DICOM PS3.16 2024d - Content Mapping Resource |
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This Annex specifies the meanings of codes defined in DICOM, either explicitly or by reference to another part of DICOM or an external reference document or standard.
The contents of this table are available in OWL, XRDF and CSV format at ftp://medical.nema.org/medical/dicom/resources/ontology/dcm/dcm.owl and in Bioportal.
Table D-1. DICOM Controlled Terminology Definitions (Coding Scheme Designator "DCM" Coding Scheme Version "01")
An acquisition device, process or method that measures autorefraction. |
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A device, process or method that stores images and other objects for a prolonged period of time. |
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An acquisition device, process or method that records images during angioscopy. |
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A device, process or method that produces assessments of the content of other instances, e.g., for quality or suitability. |
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An acquisition device, process or method that records audio. |
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An acquisition device, process or method that performs ultrasound bone densitometry. |
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An acquisition device, process or method that performs biomagnetic imaging. |
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An acquisition device, process or method that performs bone mineral densitometry by X-Ray, including dual-energy X-Ray absorptiometry (DXA) and morphometric X-Ray absorptiometry (MXA). |
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An image processing device, process or method that performs computer assisted detection or diagnosis. |
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An acquisition device, process or method that performs image capture, includes video capture. |
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An acquisition device, process or method that performs color flow Doppler. |
Replaced by (US, DCM, "Ultrasound") |
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An acquisition device, process or method that performs cinefluorography. |
Replaced by (RF, DCM, "Radiofluoroscopy") |
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An acquisition device, process or method that performs imaging using a confocal microscope. |
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A device, process or method that performs computation as a service; includes radiotherapy planning. |
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An acquisition device, process or method that records images during culposcopy. |
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An acquisition device, process or method that performs computed radiography. |
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An acquisition device, process or method that records images during cystoscopy. |
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An acquisition device, process or method that performs computed tomography. |
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A device, process or method that produces CT device acquisition protocols. |
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An acquisition device, process or method that performs duplex Doppler. |
Replaced by (US, DCM, "Ultrasound") |
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An acquisition device, process or method that performs digital fluoroscopy. |
Replaced by (RF, DCM, "Radiofluoroscopy") |
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An acquisition device, process or method that performs diaphanography. |
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An acquisition device, process or method that performs digital microscopy. |
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An acquisition device, process or method that performs imaging of the surface of the skin using epiluminescence microscopy. |
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A device, process or method that produces documents. i.e., representations of documents as images, whether by scanning or other means. |
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A device, process or method that digitizes hardcopy documents and imports them. |
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An acquisition device, process or method that performs digital subtraction angiography. |
Replaced by (XA, DCM, "X-Ray Angiography") |
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A department-based information system (for instance, Radiology or Laboratory) that provides functions related to the management of orders received from external systems or through the department system’s user interface. This definition matches that of the DSS/OF Actor in the IHE Scheduled Workflow (SWF) Profile. |
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An acquisition device, process or method that performs digital radiography. |
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An acquisition device, process or method that performs echocardiography. |
Replaced by (US, DCM, "Ultrasound") |
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An acquisition device, process or method that performs electrocardiography. |
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An acquisition device, process or method that performs electroencephalography. |
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An acquisition device, process or method that performs electromyography. |
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An acquisition device, process or method that performs electrooculography. |
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An acquisition device, process or method that performs cardiac electrophysiology. |
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An acquisition device, process or method that records images during endoscopy. |
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An acquisition device, process or method that performs fluorescein angiography. |
Replaced by (OP, DCM, "Ophthalmic photography") |
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A device, process or method that identifies features or landmarks used to establish spatial correlation between objects or frames of reference. |
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A device, process or method that performs film digitization. |
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An acquisition device, process or method that records images during fundoscopy. |
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An acquisition device, process or method that performs general microscopy. |
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A device, process or method that creates images to be printed as hard copy. |
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An acquisition device, process or method that records hemodynamic waveforms. |
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An acquisition device, process or method that performs intra-oral radiography. |
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A device, process or method that encodes calculations for an intraocular lens. |
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An acquisition device, process or method that performs intravascular optical coherence tomography |
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An acquisition device, process or method that performs intravascular ultrasound. |
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An acquisition device, process or method that performs keratometry. |
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A device, process or method that creates Key Object Selection objects. |
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An acquisition device, process or method that performs lensometry. |
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A device, process or method that performs procedure Logging; includes cath lab logging. |
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An acquisition device, process or method that records images during laparoscopy. |
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An acquisition device, process or method that performs laser surface scanning. |
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A device, process or method that produces data (models) for use in 3D manufacturing. |
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An acquisition device, process or method that performs magnetic resonance angiography. |
Replaced by (MR, DCM, "Magnetic resonance") |
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A device, process or method that creates DICOM PS3.10 interchange media. E.g., a CD creator that is managed by the Media Creation Management Service Class. |
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A device, process or method that retrieves and imports objects from Interchange Media. |
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An acquisition device, process or method that performs mammography. |
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An acquisition device, process or method that performs magnetic resonance imaging. |
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An acquisition device, process or method that performs magnetic resonance spectroscopy. |
Replaced by (MR, DCM, "Magnetic resonance") |
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Instances need to be retrieved from relatively slow media such as optical disk or tape. |
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An acquisition device, process or method that performs nuclear medicine imaging. |
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An acquisition device, process or method that measures the axial length of the eye. |
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An acquisition device, process or method that uses an interferometric, non-invasive optical tomographic technique to image 2D slices and 3D volumes of tissue using visible and near visible frequencies. |
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An acquisition device, process or method that performs ophthalmic photography. |
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An acquisition device, process or method that measures corneal topography, corneal or retinal thickness, and other similar parameters that are typically displayed as maps. |
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An acquisition device, process or method that measures the refractive characteristics of the eye. |
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An acquisition device, process or method that performs tomography of the eye that is based on light and optical principles. Tomography based on other principles, such as ultrasound, is excluded. |
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An acquisition device, process or method that performs B-scan volume analysis of tomography images of the eye based on light and optical principles. Tomography based on other principles, such as ultrasound, is excluded. |
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An acquisition device, process or method that creates en face tomography images of the eye based on light and optical principles. Tomography based on other principles, such as ultrasound, is excluded. |
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An acquisition device, process or method that measures visual fields and perform visual perimetry. |
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An acquisition device, process or method that performs optical surface scanning. |
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An acquisition device, process or method that performs imaging by means of tissue excitation through the absorption of short light pulses and detection of the resultant acoustic emission. |
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A device, process or method that produces treatment plans, e.g., delivery instructions for RT. |
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A device or sensor measuring the orientation of the patient’s body. |
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A device, process or method that creates Presentation State objects. |
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Hard Copy Print Server; includes printers with embedded DICOM print server. |
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An acquisition device, process or method that performs positron emission tomography (PET). |
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An acquisition device, process or method that performs panoramic X-Rays. |
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An image processing device, process or method that creates Registration objects. |
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A device, process or method that produces waveforms of electrical signals from the patient’s respiratory system. |
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An acquisition device, process or method that performs radiofluoroscopy. |
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An acquisition device, process or method that performs radiographic imaging (conventional film/screen). |
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A device, process or method that delivers radiation therapy; includes linear accelerator, proton therapy. |
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An acquisition device, process or method that performs radiotherapy imaging; includes portal imaging. |
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A device, process or method that produces radiotherapy plans. |
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A device, process or method that records radiotherapy treatment records. |
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A device, process or method that produces Radiotherapy Structure Sets. |
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A device, process or method that produces mappings between image pixel values and some real-world values. |
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An image processing device, process or method that performs segmentation. |
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An acquisition device, process or method that performs slide microscopy. |
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A device, process or method that records relationships between stereometric image pairs. |
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A device, process or method that creates Structured Report documents. |
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An acquisition device, process or method that records subjective refraction. |
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An acquisition device, process or method that performs single-photon emission computed tomography (SPECT). |
Replaced by (NM, DCM, "Nuclear Medicine") |
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A device, process or method that applies, in an automated manner, a stain, or reagent, to microscopy slides in preparation for imaging. |
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A device, process or method that produces texture maps. E.g., for use in 3D manufacturing. |
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An acquisition device, process or method that performs thermography. |
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An acquisition device, process or method that performs ultrasound. |
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An acquisition device, process or method that measures visual acuity. |
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An acquisition device, process or method that measures videofluorography. |
Replaced by (RF, DCM, "Radiofluoroscopy") |
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A device, process or method that digitizes video tape and imports it. |
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A networked computer equipped with a display and software for performing specific types of work, generally intended to be operated by a single user. |
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An acquisition device, process or method that performs X-Ray angiography. |
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An acquisition device, process or method that performs photography with an external camera. |
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A signal transmitted for the purpose of interchange of the current time, not specific to any source or methodology. |
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A signal that is generated for each detection of a heart beat. |
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A signal transmitted by the Inter-Range Instrumentation Group for the purpose of synchronizing time clocks. |
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A signal that indicates that X-Ray source has been activated for fluoroscopy use. |
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A signal that indicated that the X-Ray source has been activated for image recording. |
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An electrophysiological recording from the HIS nerve bundle. |
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An electrical signal from one electrode relative to an indifferent potential. |
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Electrophysiological signals acquired using a multi-splined catheter each equipped with multiple electrodes. |
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Electrophysiological signals acquired using a steerable catheter. |
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A signal point that is 35% of the peak thermal cardiac output signal. |
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A signal point that is 70% of the peak thermal cardiac output signal. |
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The peak pressure of each heart beat in the atrium caused by the atrial contraction. |
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An identified cardiac beat used in the determination of a measurement. |
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An identified cardiac beat not used in the determination of a measurement. |
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Retired. Replaced by (314453003, SCT, "Average diastolic blood pressure") |
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The lowest pressure value excluding any undershoot artifact. |
Retired. Replaced by (314451001, SCT, "Minimum diastolic blood pressure") |
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The moment at the end of the diastolic phase of the cardiac cycle. |
Retired. Replaced by (416190007, SCT, "End diastole") |
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The average blood pressure value, generally over 2 or more seconds |
Retired. Replaced by (6797001, SCT, "Mean blood pressure") |
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The peak change in blood temperature during a thermal cardiac output measurement. |
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The first discernible blood temperature change following the injectate during a thermal cardiac output measurement. |
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The average of several systolic blood pressure measurements. |
Retired. Replaced by (314440001, SCT, "Average systolic blood pressure") |
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The highest systolic blood pressure value excluding any overshoot artifact |
Retired. Replaced by (314439003, SCT, "Maximum systolic blood pressure") |
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The peak pressure of each heart beat in the atrium caused by the filling of the atrium. |
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The moment in the cardiac cycle when the HIS bundle nerves depolarize. |
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The first negative deflection of the electrocardiogram cause by ventricular depolarization. |
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The first positive deflection the electrocardiogram cause by ventricular depolarization. |
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The beginning of the second atrial contraction of two consecutive beats. |
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The stimulation interval during cardiac stimulation first used in a pacing train. |
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The stimulation interval different from the first stimulation interval used in a pacing train. |
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A stimulation interval different from and subsequent to the second interval in a pacing train. |
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Describes a stimulation interval different from and subsequent to the third interval in a pacing train. |
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The electrocardiogram deflection caused by ventricular repolarization. |
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The peak pressure of each heart beat monitored in the atrium caused by the filling of the atrium. |
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A description of the physiological condition of the patient. |
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The exercise level during a progressive cardiac stress test. |
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A series of physiological challenges designed to progressively increase the work of the heart. |
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Retired. Replaced by (129085009, SCT, "Catheterization Procedure Phase") |
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The subpart of a cardiac catheterization procedure in which a radio-opaque contrast medium is injected into the patient. |
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Physical changes administered to a patient in order to elicit an physiological response. |
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Retired. Replaced by (416430001, SCT, "End systole") |
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Time for a median particle to travel from point of injection to point of detection. |
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Total time for the acquisition is shorter than cardiac cycle, no gating is applied; see Cardiac Synchronization Technique (0018,9037). |
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Certain thresholds have been set for a gating window that defines the acceptance of measurement data during the acquisition; see Cardiac Synchronization Technique (0018,9037). |
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Certain thresholds have been set for a gating window that defines the acceptance of measurement data after the acquisition; see Cardiac Synchronization Technique (0018,9037). |
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There is a constant RR interval, which makes thresholding not required; see Cardiac Synchronization Technique (0018,9037). E.g., Pacemaker. |
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Imaging after injection of tracer during increased cardiac workload or increased myocardial blood flow, achieved by either exercise or pharmacologic means. |
Retired. Replaced by (432655005, SCT, "Cardiac stress state"). |
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Imaging after injection of additional tracer under resting conditions. |
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Imaging after allowing a moderate amount of time for tracer to move from its initial sites of uptake. Example: For Thallium imaging this would correspond to imaging 2-6 hours after injection. |
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Imaging after allowing an extended amount of time for tracer to move from its initial sites of uptake. Example: For Thallium imaging this would correspond to imaging more than 6 hours after injection. |
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Retired. Replaced by (434161005, SCT, "Peak stress state") |
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Retired. Replaced by (432554001, SCT, "Cardiac stress Recovery state") |
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Equipment that originally acquired the data stored within composite instances. E.g., a CT, MR or Ultrasound modality. |
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Equipment that has processed composite instances to create new composite instances. E.g., a workstation or software component that performs 3D construction, segmentation or applies an AI model. |
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Equipment that has modified existing composite instances (without creating new composite instances). E.g., a QA Station or Archive. |
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Equipment that has modified an existing composite instance to remove patient identifying information. |
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Equipment that has processed composite instances to create new composite instances by extracting selected frames from the original instance. |
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Equipment that has processed composite instances to create new composite instances by converting classic single frame images to enhanced multi-frame image, or vice versa and updating other instances to maintain referential integrity. |
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May include the patient's voice, or the voice of staff present in the room, or an operator's voice (whether for the purpose of recording a narrative accompanying a procedure or not). |
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The voice of a device operator, recorded during a procedure. |
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The ambient sound recorded during a procedure, which may or may not include voice and other types of sound. |
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May include the sound of the heart, but also sound from other organs, such as bowel sounds or bruits from vessels, or sounds of respiration. Not intended to include voice. |
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A digitized signal from the patient arterial system collected through pulse oximetry or other means. |
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A digitized signal from the patient respiratory system representing respiration. |
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The occasion on which a procedure was performed on admission to a specialist unit. E.g., intensive care. |
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The occasion on which a procedure was performed on discharge from hospital as an in-patient. |
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The occasion on which a procedure was performed on discharge from a specialist unit. E.g., intensive care. |
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The occasion on which a procedure was performed immediately prior to non-surgical intervention. E.g, percutaneous angioplasty, biopsy. |
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The occasion on which a procedure was performed immediately after to non-surgical intervention. E.g, percutaneous angioplasty, biopsy. |
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The occasion on which a procedure was performed at the most recent outpatient visit. |
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Evaluation of overall image quality as described in section 7.3.2 of [IEC 62563-1]. |
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Visual verification of sufficient grayscale resolution based on 8 and 10-bit markers as described in section 7.3.3 of [IEC 62563-1]. |
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Visual evaluation of luminance response using the TG18-CT test pattern as described in section 7.3.4 of [IEC 62563-1]. |
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Visual detection of luminance non-uniformities as described in section 7.3.5 of [IEC 62563-1]. |
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Visual verification of color uniformity as described in section 7.3.6 of [IEC 62563-1]. |
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Visual detection of defective pixels on dark (TG18-UN80) and bright (TG18-UN10) images as described in section 7.3.7 of [IEC 62563-1]. |
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Visual evaluation of veiling glare by looking at low contrast objects on 2 test patterns as described in section 7.3.8 of [IEC 62563-1]. |
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Visual evaluation of geometry, phase/clock correction and clipping as described in section 7.3.9 of [IEC 62563-1]. |
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Visual evaluation of viewing angle as described in section 7.3.10 of [IEC 62563-1]. |
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Visual evaluation of the appearance of clinical images as described in section 7.3.11 of [IEC 62563-1]. |
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AAPM TG18-QC Pattern used for evaluation of resolution, luminance, distortion, artifacts. See [AAPM OR 03]. |
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AAPM TG18-BR Pattern used for the evaluation of the display of low-contrast, fine-detail image structures See [AAPM OR 03]. |
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AAPM TG18-PQC Pattern used for evaluation of resolution, luminance, contrast transfer for prints. See [AAPM OR 03]. |
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AAPM TG18-CT Pattern used for evaluation of luminance response. See [AAPM OR 03]. |
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The 1st image in the AAPM TG18-LN8 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 2nd image in the AAPM TG18-LN8 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 3rd image in the AAPM TG18-LN8 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 4th image in the AAPM TG18-LN8 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 5th image in the AAPM TG18-LN8 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 6th image in the AAPM TG18-LN8 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 7th image in the AAPM TG18-LN8 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 8th image in the AAPM TG18-LN8 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 9th image in the AAPM TG18-LN8 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 10th image in the AAPM TG18-LN8 set used for DICOM grayscale calibration series. See [AAPM OR 03]. |
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The 11th image in the AAPM TG18-LN8 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 12th image in the AAPM TG18-LN8 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 13th image in the AAPM TG18-LN8 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 14th image in the AAPM TG18-LN8 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 15th image in the AAPM TG18-LN8 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 16th image in the AAPM TG18-LN8 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 17th image in the AAPM TG18-LN8 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 18th image in the AAPM TG18-LN8- set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 1st image in the AAPM TG18-LN12 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 2 nd image in the AAPM TG18-LN12 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 3rd image in the AAPM TG18-LN12 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 4th image in the AAPM TG18-LN12 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 5th image in the AAPM TG18-LN12 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 6th image in the AAPM TG18-LN12 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 7th image in the AAPM TG18-LN12 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 8th image in the AAPM TG18-LN12 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 9th image in the AAPM TG18-LN12 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 10th image in the AAPM TG18-LN12 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 11th image in the AAPM TG18-LN12 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 12th image in the AAPM TG18-LN12 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 13th image in the AAPM TG18-LN12 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 14th image in the AAPM TG18-LN12 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 15th image in the AAPM TG18-LN12 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 16th image in the AAPM TG18-LN12 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 17th image in the AAPM TG18-LN12 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The 18th image in the AAPM TG18-LN12 set used for DICOM grayscale calibration. See [AAPM OR 03]. |
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The AAPM TG18-UN10 Pattern used for evaluation of luminance and color uniformity, and angular response. See [AAPM OR 03]. |
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The AAPM TG18-UN80 Pattern used for evaluation of luminance and color uniformity, and angular response. See [AAPM OR 03]. |
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The AAPM TG18-UNL10 Pattern is the AAPM TG-18 UN10 Pattern with added defining lines. See [AAPM OR 03]. |
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The AAPM TG18-UNL80 Pattern is the AAPM TG-18 UN80 Pattern with added defining lines. See [AAPM OR 03]. |
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The AAPM TG18-AD Pattern used for visual evaluation of the reflection of ambient light from the display. See [AAPM OR 03]. |
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The AAPM TG18-MP Pattern used for evaluation of Luminance response (bit-depth resolution). See [AAPM OR 03]. |
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The AAPM TG18-RH10 Pattern used for LSF-line spectra function-(1k and 2k) evaluation by 5 horizontal lines at 10% luminance level. See [AAPM OR 03]. |
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The AAPM TG18-RH50 Pattern used for LSF-line spectra function-(1k and 2k) evaluation by 5 horizontal lines at 50% luminance level. See [AAPM OR 03]. |
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The AAPM TG18-RH89 Pattern used for LSF-line spectra function-(1k and 2k) evaluation by 5 horizontal lines at 89% luminance level. See [AAPM OR 03]. |
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The AAPM TG18-RV10 Pattern used for LSF-line spectra function-(1k and 2k) evaluation by 5 vertical lines at 10% luminance level. See [AAPM OR 03]. |
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The AAPM TG18-RV50 Pattern used for LSF-line spectra function-(1k and 2k) evaluation by 5 vertical lines at 50% luminance level. See [AAPM OR 03]. |
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The AAPM TG18-RV89 Pattern used for LSF-line spectra function-(1k and 2k) evaluation by 5 vertical lines at 89% luminance level. See [AAPM OR 03]. |
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The AAPM TG18-PX Pattern used for the assessment of display resolution. See [AAPM OR 03]. |
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The AAPM TG18-CX Pattern used to assess display resolution and resolution uniformity. See [AAPM OR 03]. |
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The AAPM TG18-LPH10 Pattern used to assess display resolution. This pattern has horizontal bars consisting of alternating single-pixel-wide lines across the faceplate of display. The lines have a 12% positive contrast against 10% background level of the maximum pixel value. See [AAPM OR 03]. |
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The AAPM TG18-LPH50 Pattern used to assess display resolution. This pattern has horizontal bars consisting of alternating single-pixel-wide lines across the faceplate of display. The lines have a 50% positive contrast against 10% background level of the maximum pixel value. See [AAPM OR 03]. |
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The AAPM TG18-LPH89 Pattern used to assess display resolution. This pattern has horizontal bars consisting of alternating single-pixel-wide lines across the faceplate of display. The lines have a 12% positive contrast against 89% background level of the maximum pixel value. See [AAPM OR 03]. |
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The AAPM TG18-LPV10 Pattern used to assess display resolution. This pattern has vertical bars consisting of alternating single-pixel-wide lines across the faceplate of display. The lines have a 12% positive contrast against 10% background level of the maximum pixel value. See [AAPM OR 03]. |
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The AAPM TG18-LPV50 Pattern used to assess display resolution. This pattern has vertical bars consisting of alternating single-pixel-wide lines across the faceplate of display. The lines have a 12% positive contrast against 50% background level of the maximum pixel value. See [AAPM OR 03]. |
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The AAPM TG18-LPV89 Pattern used to assess display resolution. This pattern has vertical bars consisting of alternating single-pixel-wide lines across the faceplate of display. The lines have a 12% positive contrast against 89% background level of the maximum pixel value. See [AAPM OR 03]. |
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The AAPM TG18-AFC Pattern used to assess display noise. See [AAPM OR 03] |
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The AAPM TG18-NS10 Pattern is AAPM TG18-RV10/RH10 with only difference being the absence of the single line at the center of the measurement area. See [AAPM OR 03]. |
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The AAPM TG18-NS50 Pattern is AAPM TG18-RV50/RH50 with only difference being the absence of the single line at the center of the measurement area. See [AAPM OR 03]. |
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The AAPM TG18-NS89 Pattern is AAPM TG18-RV89/RH89 with only difference being the absence of the single line at the center of the measurement area. See [AAPM OR 03]. |
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The TG18-GV Pattern used to assess display veiling. See [AAPM OR 03]. |
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The TG18-GVN Pattern used to assess display veiling. This pattern is identical to AAPM TG18-GV Pattern except that the large-diameter white circle is replaced with a black circle, creating a completely black pattern except for the presence of low-contrast targets. See [AAPM OR 03]. |
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The TG18-GQ Pattern used for quantitative assessment of veiling glare. This pattern is identical to TG18-GV except that is lacks the central low-contrast objects. See [AAPM OR 03]. |
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TG18-GQN Pattern used for the quantitative assessment of veiling glare. This pattern is identical to AAPM TG18-GQ Pattern except that the large-diameter white circle is replaced with a black circle, creating a completely black pattern except for the presence of low-contrast targets. See [AAPM OR 03]. |
|||
The TG18-GQB Pattern used for the quantitative assessment of veiling glare. This pattern is identical to AAPM TG18-GQ Pattern except eliminating the central black circle. See [AAPM OR 03]. |
|||
The TG18-GA03 Pattern used for quantitative assessment of veiling glare. This pattern is identical to TG18-GQ except that the radius of the central black circle is varied as r = 3. See [AAPM OR 03]. |
|||
The TG18-GA05 Pattern This pattern is identical to TG18-GQ except that the radius of the central black circle is varied as r = 5. See [AAPM OR 03]. |
|||
The TG18-GA08 Pattern used for quantitative assessment of veiling glare. This pattern is identical to TG18-GQ except that the radius of the central black circle is varied as r = 8. See [AAPM OR 03]. |
|||
The TG18-GA10 Pattern used for quantitative assessment of veiling glare. This pattern is identical to TG18-GQ except that the radius of the central black circle is varied as r = 10. See [AAPM OR 03]. |
|||
The TG18-GA15 Pattern used for quantitative assessment of veiling glare. This pattern is identical to TG18-GQ except that the radius of the central black circle is varied as r = 15. |
|||
The TG18-GA20 Pattern used for quantitative assessment of veiling glare. This pattern is identical to TG18-GQ except that the radius of the central black circle is varied as r = 20. See [AAPM OR 03]. |
|||
The TG18-GA25 Pattern used for quantitative assessment of veiling glare. This pattern is identical to TG18-GQ except that the radius of the central black circle is varied as r = 25. See [AAPM OR 03]. |
|||
The TG18-GA30 Pattern used for quantitative assessment of veiling glare. This pattern is identical to TG18-GQ except that the radius of the central black circle is varied as r = 30. See [AAPM OR 03]. |
|||
The AAPM TG18-CH Image is a reference anatomical PA chest image. See [AAPM OR 03]. |
|||
The AAPM TG18-KN Image is a reference anatomical knee image. See [AAPM OR 03]. |
|||
The AAPM TG18-MM1 Image is a reference anatomical mammogram image. See [AAPM OR 03]. |
|||
The AAPM TG18-MM2 Image is a reference anatomical mammogram image. See [AAPM OR 03]. |
|||
The IEC OIQ Pattern is used as an alternative to the TG18-QC Pattern. See [IEC 62563-1]. |
|||
The IEC ANG Pattern used for angular viewing evaluation. See [IEC 62563-1]. |
|||
The IEC GD Pattern used for geometrical image evaluation. See [IEC 62563-1]. |
|||
The IEC BN01 Pattern is used as an alternative to the TG18-LN-01 Pattern, to avoid the use of a cone or baffle with LCDs. See [IEC 62563-1]. |
|||
The IEC BN02 Pattern is used as an alternative to the TG18-LN-02 Pattern, to avoid the use of a cone or baffle with LCDs. See [IEC 62563-1]. |
|||
The IEC BN03 Pattern is used as an alternative to the TG18-LN-03 Pattern, to avoid the use of a cone or baffle with LCDs. See [IEC 62563-1]. |
|||
The IEC BN04 Pattern is used as an alternative to the TG18-LN-04 Pattern, to avoid the use of a cone or baffle with LCDs. See [IEC 62563-1]. |
|||
The IEC BN05 Pattern is used as an alternative to the TG18-LN-05 Pattern, to avoid the use of a cone or baffle with LCDs. See [IEC 62563-1]. |
|||
The IEC BN06 Pattern is used as an alternative to the TG18-LN-06 Pattern, to avoid the use of a cone or baffle with LCDs. See [IEC 62563-1]. |
|||
The IEC BN07 Pattern is used as an alternative to the TG18-LN-07 Pattern, to avoid the use of a cone or baffle with LCDs. See [IEC 62563-1]. |
|||
The IEC BN08 Pattern is used as an alternative to the TG18-LN-08 Pattern, to avoid the use of a cone or baffle with LCDs. See [IEC 62563-1]. |
|||
The IEC BN09 Pattern is used as an alternative to the TG18-LN-09 Pattern, to avoid the use of a cone or baffle with LCDs. See [IEC 62563-1]. |
|||
The IEC BN10 Pattern is used as an alternative to the TG18-LN-10 Pattern, to avoid the use of a cone or baffle with LCDs. See [IEC 62563-1]. |
|||
The IEC BN11 Pattern is used as an alternative to the TG18-LN-11 Pattern, to avoid the use of a cone or baffle with LCDs. See [IEC 62563-1]. |
|||
The IEC BN12 Pattern is used as an alternative to the TG18-LN-12 Pattern, to avoid the use of a cone or baffle with LCDs. See [IEC 62563-1]. |
|||
The IEC BN13 Pattern is used as an alternative to the TG18-LN-13 Pattern, to avoid the use of a cone or baffle with LCDs. See [IEC 62563-1]. |
|||
The IEC BN14 Pattern is used as an alternative to the TG18-LN-14 Pattern, to avoid the use of a cone or baffle with LCDs. See [IEC 62563-1]. |
|||
The IEC BN15 Pattern is used as an alternative to the TG18-LN-15 Pattern, to avoid the use of a cone or baffle with LCDs. See [IEC 62563-1]. |
|||
The IEC BN16 Pattern is used as an alternative to the TG18-LN-16 Pattern, to avoid the use of a cone or baffle with LCDs. See [IEC 62563-1]. |
|||
The IEC BN17 Pattern is used as an alternative to the TG18-LN-17 Pattern, to avoid the use of a cone or baffle with LCDs. See [IEC 62563-1]. |
|||
The IEC BN18 Pattern is used as an alternative to the TG18-LN-18 Pattern, to avoid the use of a cone or baffle with LCDs. See [IEC 62563-1]. |
|||
Test image "Bild 2" for the gray-scale reproduction of imaging devices. See [DIN 6868-57]. |
|||
Test image "Bild 3" for the geometrical imaging properties of imaging devices. See [DIN 6868-57]. |
|||
Test image "Bild 5" for displaying the spatial and contrast resolution as well as the line structure of imaging devices. See [DIN 6868-57]. |
|||
An alternative to AAPM TG18-UN80, specified at 100% of maximum pixel value. |
|||
A standard display test pattern. See [SMPTE RP133]. A pattern is available at http://www.dclunie.com/images/smpte.512.512.8.gif. |
|||
A Display Device that displays images on a Cathode Ray Tube. |
|||
A Display Device that displays images on a Liquid Crystal Display. |
|||
A Display Device that displays images on an Organic Light Emitting Diode based display. |
|||
A Display Device that projects images on a surface from behind using a Digital Light Processing Projector. |
|||
A Display Device that projects images on a surface from in front using a Digital Light Processing Projector. |
|||
A Display Device that projects images on a surface from behind using a Cathode Ray Tube. |
|||
A Display Device that projects images on a surface from in front using a Cathode Ray Tube. |
|||
A Display Device that projects images on a surface from an unspecified direction using an unspecified means. |
|||
The work item task is to prepare a report that contains the interpretation of an imaging study. |
|||
The procedure to read DICOM instances from DICOM interchange media, coerce identifying Attributes into the local namespace if necessary, and make the instances available. |
|||
Digitization of pages of a paper document (Units may be specified as Pages, Documents). |
|||
A device that connects using the USB hard drive interface. These may be USB-Sticks, portable hard drives, and other technologies. |
|||
Email and email attachments used as a media for data transport. |
|||
DVD, DVD-RAM, and other DVD formatted media used for data transport. |
|||
Audit event: DICOM Instances have been created, read, updated, or deleted -audit event. |
|||
Audit event: Order has been created, read, updated or deleted. |
|||
Audit event: Patient Record has been created, read, updated, or deleted. |
|||
Audit event: Procedure Record has been created, read, updated, or deleted. |
|||
Audit event: A use of a restricted function has been attempted. |
|||
Audit event: Security attributes of an object have been changed. |
|||
Audit event: Security attributes of a user have been changed. |
|||
Audit participant role ID of software application launcher, i.e., the entity that started or stopped an application. |
|||
Audit participant role ID of media receiving data during an export. |
|||
Audit participant role ID of media providing data during an import. |
|||
ID of a node that is a participant object of an audit message. |
|||
System, organization, agency, or department that has assigned an instance identifier (such as placer or filler number, patient or provider identifier, etc.). |
|||
Procedure order canceled by requesting physician or other authorized physician. |
|||
Procedure discontinued due to incorrect procedure being ordered. |
|||
Procedure discontinued due to patient allergy to media/contrast (reported or reaction). |
|||
Procedure discontinued due to patient refusal to continue procedure. |
|||
Procedure discontinued due to patient being taken for treatment or surgery. |
|||
Procedure discontinued due to patient pregnancy (reported or determined). |
|||
Procedure discontinued to restart with new procedure code for correct charging. |
|||
Procedure discontinued due to duplicate orders received for same procedure. |
|||
Procedure discontinued due to incorrect side (laterality) being ordered. |
|||
Procedure discontinued due to incorrect patient or procedure step selected from modality worklist. |
|||
Procedure step is discontinued to change to other equipment or modality. |
|||
A movement of the patient preventing continuation of procedure or affecting result quality. |
|||
An error of the operator preventing continuation of procedure or affecting result quality. |
|||
The brachytherapy channel is obstructed and the treatment in this channel cannot proceed. |
|||
One or more objects associated with the object set is missing. |
|||
Procedure discontinued due to necessary equipment, staff or other resource becoming (temporarily) unavailable to the procedure. |
|||
Procedure discontinued due to necessary equipment, staff or other resource being inadequate to complete the procedure. |
|||
A new Procedure Step has been scheduled to replace the Discontinued Procedure Step. |
|||
It is recommended that a new Procedure Step be scheduled to replace the Discontinued Procedure Step. |
|||
The resource to which a workitem has been assigned has rejected the assignment. |
|||
Reporting not possible due to lack of quality of the images provided. |
|||
The nature of the clinical problem means that reporting of the study requires a subject matter expert. |
|||
Ventral structures of the diencephalon that cannot readily be distinguished on MR imaging, including the hypothalamus, mammillary body, subthalamic nuclei, substantia nigra, red nucleus, lateral geniculate nucleus, medial geniculate nucleus, zona incerta, cerebral peduncle, lenticular fasciculus, medial lemniscus, and optic tract. See http://neuromorphometrics.org:8080/Seg/html/segmentation/ventral%20diencephalon.html and http://www.cma.mgh.harvard.edu/manuals/segmentation/. |
|||
Area(s) of reduced intensity on T1 weighted images relative to the surrounding white matter. These may be indicative of age-related or neurodegenerative white matter lesions, and may be co-located with areas of white matter T2 hyperintensity, but the concept is specifically confined to the MR appearance on T1 weighted images. |
|||
Area(s) of increased intensity on T2 weighted images relative to the surrounding white matter. These may be indicative of age-related or neurodegenerative white matter lesions, and may be co-located with areas of white matter T1 hypointensity, but the concept is specifically confined to the MR appearance on T2 weighted images. |
|||
The dorsal component of the SLF originating from the medial and dorsal parietal cortex and ending in the dorsal and medial part of the frontal lobe. See Makris N, et al. "Segmentation of Subcomponents within the Superior Longitudinal Fascicle in Humans: A Quantitative, In Vivo, DT-MRI Study." Cerebral Cortex 15, no. 6 (June 1, 2005): 854-69. doi:10.1093/cercor/bhh186. |
|||
The major component of the SLF, derived from the caudal-inferior parietal region corresponding to the angular gyrus in the human and terminating within the dorsolateral frontal region. See Makris N, et al. "Segmentation of Subcomponents within the Superior Longitudinal Fascicle in Humans: A Quantitative, In Vivo, DT-MRI Study." Cerebral Cortex 15, no. 6 (June 1, 2005): 854-69. doi:10.1093/cercor/bhh186. |
|||
The ventral component of the SLF, originating from the supramarginal gyrus and terminating predominantly in the ventral premotor and prefrontal areas. See Makris N, et al. "Segmentation of Subcomponents within the Superior Longitudinal Fascicle in Humans: A Quantitative, In Vivo, DT-MRI Study." Cerebral Cortex 15, no. 6 (June 1, 2005): 854-69. doi:10.1093/cercor/bhh186. |
|||
White matter that surrounds a lesion of interest. E.g., to identify the otherwise unclassified white matetr that surrounds a tumor to be surgically resected. |
|||
Signal intensity of a Spin tagging Perfusion MR image. Spin tagging is a technique for the measurement of blood perfusion, based on magnetically labeled arterial blood water as an endogenous tracer. |
|||
Signal intensity of a Time-of-flight (TOF) MR image. Time-of-flight (TOF) is based on the phenomenon of flow-related enhancement of spins entering into an imaging slice. As a result of being unsaturated, these spins give more signal that surrounding stationary spins. |
|||
Signal intensity of a Proton Density Weighted MR image. All MR images have intensity proportional to proton density. Images with very little T1 or T2 weighting are called 'PD-weighted'. |
|||
Signal intensity of T1 Weighted MR image. A T1 Weighted MR image is created typically by using short TE and TR times. |
|||
Signal intensity of a T2 Weighted MR image. T2 Weighted image contrast state is approached by imaging with a TR long compared to tissue T1 (to reduce T1 contribution to image contrast) and a TE between the longest and shortest tissue T2s of interest. |
|||
Signal intensity of a T2* Weighted MR image. The T2* phenomenon results from molecular interactions (spin spin relaxation) and local magnetic field non-uniformities, which cause the protons to precess at slightly different frequencies. |
|||
Signal intensity of a Field Map MR image. A Field Map MR image provides a direct measure of the B 0 inhomogeneity at each point in the image. |
|||
Coefficient reflecting the fractional anisotropy of the tissues, derived from a diffusion weighted MR image. Fractional anisotropy is proportional to the square root of the variance of the Eigen values divided by the square root of the sum of the squares of the Eigen values. |
Basser PJ, Pierpaoli C. Microstructural and physiological features of tissues elucidated by quantitative-diffusion-tensor MRI. J Magn Reson B. 1996 Jun;111(3):209-19. http://citeseerx.ist.psu.edu/viewdoc/download?doi=10.1.1.162.2222&rep=rep1&type=pdf |
||
Coefficient reflecting the relative anisotropy of the tissues, derived from a diffusion weighted MR image. |
Basser PJ, Pierpaoli C. Microstructural and physiological features of tissues elucidated by quantitative-diffusion-tensor MRI. J Magn Reson B. 1996 Jun;111(3):209-19. http://citeseerx.ist.psu.edu/viewdoc/download?doi=10.1.1.162.2222&rep=rep1&type=pdf |
||
Dxx Component of the diffusion tensor, quantifying the molecular mobility along the X axis. |
|||
Dxy Component of the diffusion tensor, quantifying the correlation of molecular displacements in the X and Y directions. |
|||
Dxz Component of the diffusion tensor, quantifying the correlation of molecular displacements in the X and Z directions. |
|||
Dyy Component of the diffusion tensor, quantifying the molecular mobility along the Y axis. |
|||
Dyz Component of the diffusion tensor, quantifying the correlation of molecular displacements in the Y and Z directions. |
|||
Dzz Component of the diffusion tensor, quantifying the molecular mobility along the Z axis. |
|||
Signal intensity of a T1 Weighted Dynamic Contrast Enhanced MR image. A T1 Weighted Dynamic Contrast Enhanced MR image reflects the dynamics of diffusion of the exogenous contrast media from the blood pool into the extra vascular extracellular space (EES) of the brain at a rate determined by the blood flow to the tissue, the permeability of the Brain Blood Barrier (BBB), and the surface area of the perfusing vessels. |
|||
Signal intensity of a T2 Weighted Dynamic Contrast Enhanced MR image. A T2 Weighted Dynamic Contrast Enhanced MR image reflects the T2 of tissue decrease as the Gd contrast agent bolus passes through the brain. |
|||
Signal intensity of a T2* Weighted Dynamic Contrast Enhanced MR image. A T2* Weighted Dynamic Contrast Enhanced MR image reflects the T2* of tissue decrease as the Gd contrast agent bolus passes through the brain. |
|||
Signal intensity of a Blood Oxygenation Level image. Used in Photoacoustic Imaging and functional MR. In functional MR BOLD imaging it is used for detecting brain activation and is sensitive to blood oxygenation (but also to cerebral blood flow and volume). |
|||
Accumulated decay event counts in a nuclear medicine projection image. |
|||
Accumulated decay event counts in a Nuclear Medicine Tomographic image (including PET). |
|||
Spatial Displacement along axis X of a non linear deformable spatial registration image. The X axis is defined in reference to the patient's orientation, and is increasing to the left hand side of the patient. |
|||
Spatial Displacement along axis Y of a non linear deformable spatial registration image. The Y axis is defined in reference to the patient's orientation, and is increasing to the posterior side of the patient. |
|||
Spatial Displacement along axis Z of a Non linear deformable spatial registration image. The Z axis is defined in reference to the patient's orientation, and is increasing toward the head of the patient. |
|||
Measured resistance to the flow of blood. E.g., through the vasculature or through a heart value. |
|||
Measured resistance to the flow of blood. E.g., through the vasculature or through a heart value, normalized to a particular indexed scale. |
|||
Scalar value related to the elastic properties of the tissue. |
|||
Scalar value related to the volume of blood perfusing into tissue. |
|||
Y (Luminance) component of a YBR FULL image, as defined in JPEG 2000. |
|||
CB (Blue chrominance) component of a YBR FULL image, as defined in JPEG 2000. |
|||
CR (Red chrominance) component of a YBR FULL image, as defined in JPEG 2000. |
|||
Y (Luminance) component of a YBR PARTIAL image, as defined in JPEG 2000. |
|||
CB (Blue chrominance) component of a YBR PARTIAL image, as defined in JPEG 2000. |
|||
CR (Red chrominance) component of a YBR PARTIAL image, as defined in JPEG 2000. |
|||
Y (Luminance) component of a YBR ICT image (Irreversible Color Transform), as defined in JPEG 2000. |
|||
CB (Blue chrominance) component of a YBR ICT image (Irreversible Color Transform), as defined in JPEG 2000. |
|||
CR (Red chrominance) component of a YBR ICT image (Irreversible Color Transform), as defined in JPEG 2000. |
|||
Y (Luminance) component of a YBR RCT image (Reversible Color Transform), as defined in JPEG 2000. |
|||
CB (Blue chrominance) component of a YBR RCT image (Reversible Color Transform), as defined in JPEG 2000. |
|||
CR (Red chrominance) component of a YBR RCT image (Reversible Color Transform), as defined in JPEG 2000. |
|||
The ability of a material to create an ultrasound return echo. |
|||
Decrease in the number of photons in an X-Ray beam due to interactions with the atoms of a material substance. Attenuation is due primarily to two processes, absorption and scattering. |
|||
Coefficient that describes the fraction of a beam of X-Rays or gamma rays that is absorbed or scattered per unit thickness of the absorber. This value basically accounts for the number of atoms in a cubic cm volume of material and the probability of a photon being scattered or absorbed from the nucleus or an electron of one of these atoms. |
Retired. Replaced by (112031, DCM, "Attenuation Coefficient"). |
||
Binary value denoting that the segmented property is present. |
|||
Probability, defined as a percentage, that the segmented property occupies the spatial area defined by the voxel. |
|||
Percentage of the voxel area occupied by the segmented property. |
|||
Dimension denoting the energy (frequency or wavelength) of photons. |
|||
Dimension used to sequence events, to compare the duration of events and the intervals between events. |
|||
A spatial dimension axis running along a line between the patient's left and right side. |
|||
A spatial dimension axis running along a line between the patient's head and foot. |
|||
A spatial dimension axis running along a line between the patient's anterior and posterior sides. |
|||
A spatial dimension axis running along a line between the apex and base of an organ, object, or chamber. |
|||
A spatial dimension axis running along a line between the anterior and inferior sides of an organ, object, or chamber. |
|||
A spatial dimension axis running along a line between the septum and wall of a chamber. |
|||
Orientation of a spatial dimension where increasing values run from the right to the left side of the patient. |
|||
Orientation of a spatial dimension where increasing values run from the left to the right side of the patient. |
|||
Orientation of a spatial dimension where increasing values run from the head to the foot of the patient. |
|||
Orientation of a spatial dimension where increasing values run from the foot to the head of the patient. |
|||
Orientation of a spatial dimension where increasing values run from the anterior to the posterior side of the patient. |
|||
Orientation of a spatial dimension where increasing values run from the posterior to the anterior side of the patient. |
|||
Orientation of a spatial dimension where increasing values run from the apex to the base. |
|||
Orientation of a spatial dimension where increasing values run from the base to the apex. |
|||
Orientation of a spatial dimension where increasing values run from the anterior to the inferior. |
|||
Orientation of a spatial dimension where increasing values run from the inferior to the anterior. |
|||
Orientation of a spatial dimension where increasing values run from the septum of a chamber to the opposite wall. |
|||
Orientation of a spatial dimension where increasing values run from the opposite wall to the septum of a chamber. |
|||
The x coordinate of the upper left hand corner (center of the first voxel transmitted) of the image, with respect to the patient-based coordinate system. |
|||
The y coordinate of the upper left hand corner (center of the first voxel transmitted) of the image, with respect to the patient-based coordinate system. |
|||
The z coordinate of the upper left hand corner (center of the first voxel transmitted) of the image, with respect to the patient-based coordinate system. |
|||
The x value of the first row direction cosine with respect to the patient, with respect to the patient-based coordinate system. |
|||
The y value of the first row direction cosine with respect to the patient, with respect to the patient-based coordinate system. |
|||
The z value of the first row direction cosine with respect to the patient, with respect to the patient-based coordinate system. |
|||
The x value of the first column direction cosine with respect to the patient, with respect to the patient-based coordinate system. |
|||
The y value of the first column direction cosine with respect to the patient, with respect to the patient-based coordinate system. |
|||
The z value of the first column direction cosine with respect to the patient, with respect to the patient-based coordinate system. |
|||
The family of algorithm(s) that best describes the software algorithm used. |
|||
The name assigned by a manufacturer to a specific software algorithm. |
|||
The input parameters used by a manufacturer to configure the behavior of a specific software algorithm. |
|||
The software version identifier assigned by a manufacturer to a specific software algorithm. |
|||
The type of correlation applied to detection results. E.g., temporal, spatial. |
|||
Assignment of intermediate or overall interpretation results to a general category. |
|||
Assessment of annotating tissues in breast; generally including fatty, mixed or dense |
Retired. Replaced by (129715009, SCT, "Breast composition"). |
||
Purpose of reference for an SCOORD Content Item that is an outline of the breast that includes the pectoral muscle tissue |
Purpose of Reference for Content Item of value type COMPOSITE or SCOORD |
||
The type of distribution associated with detected calcifications. |
|||
Identification of the morphology of detected calcifications. |
|||
May be used as the Purpose of Reference for Content Item of value type COMPOSITE or SCOORD, or a qualitative observation on an ROI. |
|||
The likelihood that the feature analyzed is in fact the type of feature identified. |
|||
The likelihood that the finding detected is in fact the type of finding identified. |
|||
The certainty that a device places on an impression, where 0 equals no certainty and 100 equals certainty. |
|||
A location identifier based on clockface numbering or anatomic subregion. |
|||
An item that is an inferred correlation relating two or more individual findings or features. |
|||
The inferred relationship between the findings or features making up a composite feature. |
|||
General assessment of whether or not CAD processing was successful, and whether any findings resulted. |
|||
A location identifier based on a feature's inferred distance from the surface of the associated anatomy. |
|||
A textual description of the change that occurred over time in a qualitative characteristic of a feature. |
|||
The type of finding sought after by a specific algorithm applied to one image. |
|||
A general change that occurred within an imaged area between a prior imaging procedure and the current imaging procedure. |
|||
A group of analysis algorithms that were attempted, but failed. |
|||
A group of detection algorithms that were attempted, but failed. |
|||
For projection radiography, the horizontal physical distance measured at the front plane of an Image Receptor housing between the center of each pixel (spacing between the centers of adjacent columns). For tomographic images, the horizontal physical distance in the patient between the center of each pixel. |
|||
Laterality of (possibly paired) body part contained in an image. |
|||
A container that references all image data used as evidence to produce a report. |
|||
A numeric value in the range 0 to 100, inclusive, where 0 is worst quality and 100 is best quality. |
|||
Purpose of reference for an SCOORD Content Item that identifies a specific region of interest within an image |
Purpose of Reference for Content Item of value type COMPOSITE or SCOORD |
||
The projection of the anatomic region of interest on an image receptor. |
|||
Free-form text describing the overall or an individual impression. |
|||
A container for a group of related results from interpretation of one or more images and associated clinical information. |
|||
The X-Ray attenuation of a lesion relative to the expected attenuation of an equal volume of fibroglandular breast tissue. |
|||
A structured report containing the results of computer-aided detection or diagnosis applied to breast imaging and associated clinical information. |
|||
The characteristic of the boundary, edges or border of a detected lesion. |
|||
The quantity of calcifications detected within an identified group or cluster. |
|||
Purpose of reference for a COMPOSITE Content Item that identifies it as the original source of evidence for another Content Item in the report |
Purpose of Reference for Content Item of value type COMPOSITE or SCOORD |
||
May be used as the Purpose of Reference for Content Item of value type COMPOSITE or SCOORD, or a qualitative observation on an ROI. |
|||
The inferred type of disease associated with an identified feature. |
|||
The patient orientation relative to the image plane, specified by a value that designates the anatomical direction of the positive column axis (top to bottom). |
|||
The patient orientation relative to the image plane, specified by a value that designates the anatomical direction of the positive row axis (left to right). |
|||
Purpose of reference for an SCOORD Content Item that is an outline of the pectoral muscle tissue only |
Purpose of Reference for Content Item of value type COMPOSITE or SCOORD |
||
Percent of breast area that is mammographically dense, excluding pectoralis muscle. |
|||
The likelihood that an identified finding or feature is cancerous. |
|||
A location identifier based on the division of an area into four regions. |
|||
A qualitative characteristic of a feature that has changed over time. |
|||
The quality control standard used to make a quality assessment. |
|||
A specific quality related deficiency detected within an image. |
|||
Recommended type of follow-up to an imaging procedure, based on interpreted results. |
|||
Recommended follow-up date to an imaging procedure, based on interpreted results. |
|||
Recommended follow-up interval to an imaging procedure, based on interpreted results. |
|||
The recommendation of the producer of a Content Item regarding presentation of the Content Item by recipients of the report. |
|||
An indication of how widespread the detection of a feature is within the analyzed image data. |
|||
A textual description of the contents of a selected region identified within an image. |
|||
Date on which the acquisition of the study information was started. |
|||
Time at which the acquisition of the study information was started. |
|||
A group of analysis algorithms that were attempted and completed successfully. |
|||
A group of detection algorithms that were attempted and completed successfully. |
|||
An overall indication of whether the CAD detection algorithms applied were completed successfully. |
|||
An overall indication of whether the CAD analysis algorithms applied were completed successfully. |
|||
For projection radiography, the vertical physical distance measured at the front plane of an Image Receptor housing between the center of each pixel (spacing between the centers of adjacent rows). For tomographic images, the vertical physical distance in the patient between the center of each pixel. |
|||
A radiographic projection that has been with the patient lying on a table with the X-Ray source on one side of the table and the detector on the other. E.g., may describe a cross-table cervical spine, chest or pelvis X-Ray image. |
|||
One of a number of discrete points on the Receiver-Operator Characteristics (ROC) curve that reflects the expected sensitivity and specificity of a CAD algorithm, where zero indicates the highest specificity, lowest sensitivity operating point. The value should not exceed the Maximum CAD Operating Point. |
|||
The maximum value of CAD Operating Point for the specific CAD algorithm used. |
|||
The number of false CAD markers per image. Correlates to inverse of Image Specificity. |
|||
The number of false markers per collection of images that are CAD processed as a group. Correlates to inverse of Case Specificity. |
|||
The percentage of cancers that should be detected by a CAD algorithm where CAD marks the cancers in at least one view. |
|||
The percentage of cancers that should be detected by a CAD algorithm where CAD marks the cancers in each view. |
|||
The percentage of cases (collections of images CAD processed as a group) without cancer that have no CAD findings whatsoever. Correlates to inverse of False Markers per Case. |
|||
The percentage of images without cancer that have no CAD findings whatsoever. Correlates to inverse of False Markers per Image. |
|||
The CAD operating point that is recommended for initial display by the creator of the structured report. |
|||
A list of CAD operating points including their corresponding characteristics. |
|||
The surface shape of all or a portion of breast related anatomy. |
|||
Image quality incorporates the following clinical image evaluation parameters: assessment of positioning, compression, artifacts, exposure, contrast, sharpness, and labeling. |
|||
A finding or feature that is identified as a non-anatomic foreign object. |
|||
A space-occupying lesion identified in a single image or projection |
Retired. Replaced by (129793001, SCT, "Mammography breast density"). |
||
Retired. Replaced by (129770007, SCT, "Individual Calcification"). |
|||
Multiple calcifications identified as occupying a small area of tissue (less than 2 cc) |
Retired. Replaced by (129769006, SCT, "Calcification Cluster"). |
||
An abnormality noted at imaging within the dermis of the breast. |
|||
An abnormality noted at imaging on the epidermis of the breast. |
|||
An assessment category to indicate that images have been acquired to assess marker placement following a breast interventional procedure. |
|||
An indication that the patient should seek post procedural follow-up directives from a clinical health care provider. |
|||
A recommendation on a patient with known cancer to take steps appropriate to the diagnosis. |
|||
Patient has previous diagnosis of breast cancer resulting in mastectomy. |
|||
Patient has a finding of mass reported on a prior imaging study. |
|||
A breast imaging procedure performed on a specific area of the breast. |
|||
A cluster of tiny anechoic foci each smaller than 2-3 mm in diameter with thin (less than 0.5 mm) intervening septations and no discrete solid components. |
|||
A fluid filled mass most commonly characterized by homogeneous low-level internal echoes on ultrasound. |
|||
A spot or coned down compression of the breast providing a reduction in the thickness and a magnification of the localized area of interest and improved separation of breast tissue. |
|||
Retired. Replaced by (16310003, SCT, "Diagnostic ultrasonography"). |
|||
Obtain previous mammography studies to compare to present study. |
|||
A medical procedure used for the sampling of mammary duct tissue |
Retired. Replaced by (18102001, SCT, "Mammary ductogram"). |
||
Follow up study at 12 months for women ≥ 40 years of age having a prior negative study and no mitigating risk factors for breast cancer. |
|||
Any decision to biopsy should be based on clinical assessment |
Any decision to perform tissue acquisition should be based on clinical assessment. |
||
Breast tissue acquisition following the identification of an area of concern with the placement of a needle or needle-wire assembly. |
|||
Pathologic analysis of breast tissue and lesions using core tissue samples. |
|||
Lesions that do not have the characteristic morphologies of breast cancer but have a definite probability of being malignant. There is a sufficient concern to urge a biopsy. |
|||
Lesions have a high probability of being cancer, which require additional action. |
|||
Presentation Required: Rendering device is expected to present |
The producer of a report intends for a recipient of the report to present or display the associated Content Item. |
||
The producer of a report considers the presentation or display of the associated Content Item by a recipient to be optional. |
|||
Not for Presentation: Rendering device expected not to present |
The producer of a report intends for a recipient of the report NOT to present or display the associated Content Item. |
||
The associated Content Items are identified as being the same finding or feature at different points in time. |
|||
The associated Content Items are identified as being the same finding or feature on different projections taken at the same point in time. |
|||
The associated Content Items are identified as being related side-to-side. |
|||
There is more than one image of the same modality in the interpreted data. |
|||
There is more than one image of the same modality in the interpreted data. |
|||
The interpreted data contains images from multiple modalities. |
|||
The fibrous tissue replacing normal tissues destroyed by disease or injury |
Retired. Replaced by (12402003, SCT, "Scar tissue"). |
||
A medical appliance used for localization of non palpable breast lesions to insure that the proper area is removed in a surgical biopsy |
Retired. Replaced by (129463006, SCT, "J Wire"). |
||
Retired. Replaced by (14106009, SCT, "Cardiac Pacemaker"). |
|||
Retired. Replaced by (129460009, SCT, "Compression paddle"). |
|||
Retired. Replaced by (228761004, SCT, "Collimator"). |
|||
An area designated on a radiographic film for facility and patient ID information |
Retired. Replaced by (129467007, SCT, "ID Plate"). |
||
This term may not be used in Context Group Extensions; see Section 7.2.3 |
|||
View and Laterality Marker does not have both view and laterality |
|||
Flash doesn't include patient name and additional patient id |
|||
Flash doesn't include cassette/screen/detector identification |
|||
MLO No fat is visualized posterior to fibroglandular tissues |
|||
CC Posterior nipple line does not measure within 1 cm of MLO |
|||
Signals that do not faithfully reproduce actual anatomic structures because of distortion or of addition or deletion of information. |
|||
Feature(s) arising from the acquisition unit's anti-scatter grid mechanism. For two-dimensional systems, such features include those of mechanically damaged or incorrectly positioned grids. For moving or Bucky grids, artifacts may result from intentional grid motion that is inadequate in duration or velocity uniformity. |
|||
Inadequate arrangement of the anatomy of interest with respect to the X-Ray field and image detector sensitive area. Examples: 1) positioning is "cutoff" when the projection of anatomy of interest falls outside the sensitive area of the detector; 2) "cone cut", in which the X-Ray field does not adequately cover the anatomy of interest; 3) detector's sensitive surface is too small to cover the projection of the anatomy of interest; 4) improper angular orientation or "rotation" of anatomy of interest with respect to the X-Ray source, or detector; 5) projection of other anatomy or clothing over the anatomy of interest in the image. |
|||
Unacceptable image blur resulting from motion of the anatomy of interest during exposure or the inadequately compensated motion of X-Ray source with respect to the image detector during exposure. |
|||
Inadequate number of quanta reached the detector during exposure. Reasons for under exposed images include low kVp, low mAs product, excess Source Image Distance. Under exposed images have inadequate signal and higher noise in the areas of interest. |
|||
An excess number of quanta reached the detector during exposure. Reasons for over exposed images include high kVp, high mAs product, short Source Image Distance. Over exposed images have high signal and lower noise in the areas of interest. Over exposed area may demonstrate lack of contrast from over saturation of the detector. |
|||
Features or discontinuities arising from causes other than the anti-scatter grid and image detector. |
|||
Failure of the device to operate according to mechanical design specifications. |
|||
Failure of a device to operate according to electrical design specifications. |
|||
Attributable to software used in generation or handling of image. |
|||
Images processed inappropriately, not following appropriate protocol. |
|||
Failure that is not mechanical or electrical or otherwise described. |
|||
The attempted process succeeded in some ways, but failed in others. |
|||
Analysis of a related group of findings or features detected during image data inspection, to produce a summary impression and/or recommendation. |
|||
Analysis of all groups of findings or features, to produce a single impression and/or recommendation. |
|||
Quality of an image renders it unusable for the intended purpose. |
|||
Quality of an image is usable for the intended purpose, but does not meet the quality control standard. |
|||
Quality of an image is usable for the intended purpose and meets the quality control standard. |
|||
An image quality control standard specified by the American College of Radiology. |
|||
An image quality control standard in the US Code of Federal Regulations. |
|||
An image quality control standard specified or adopted by the institution responsible for the document. |
|||
No findings resulted upon successful completion of all attempted computer-aided detection and/or analysis. |
|||
One or more findings resulted upon successful completion of all attempted computer-aided detection and/or analysis. |
|||
No findings resulted from the attempted computer-aided detection and/or analysis, but one or more failures occurred in the process. |
|||
One or more findings resulted from the attempted computer-aided detection and/or analysis, but one or more failures occurred in the process. |
|||
All of the attempted computer-aided detection and/or analysis failed, so there could be no findings. |
|||
A benign tumor having glandular characteristics but composed of fat, with the presence of normal mammary ducts |
Retired. Replaced by (22024005, SCT, "Adenolipoma"). |
||
Retired. Replaced by (67617000, SCT, "Ductal hyperplasia, Usual"). |
|||
Retired. Replaced by (128765009, SCT, "Adenomyoepithelioma"). |
|||
Axillary node that is normal in appearance with no associated pathology. |
|||
Excessive proliferation of normal tissue arrangement of the axillary node. |
|||
Retired. Replaced by (130963002, SCT, "Asynchronous involution of breast"). |
|||
Calcifications having typically benign morphology. They are not of intermediate or high probability of concern for malignancy. |
|||
Growing within a cystic adenoma, filling the cavity with a mass of branching epithelial processes |
Retired. Replaced by (47488001, SCT, "Intracystic papilloma"). |
||
Adenoma located in mammary duct, present as discrete sclerotic nodules, solitary or multiple. |
|||
The occurrence of fibrous tumor-forming stromal proliferation in patients with diabetes mellitus. |
|||
A deep seated firm tumor frequently occurring on the chest consisting of collagenous tissue that infiltrates surround muscle; frequently recurs but does not metastasize |
Retired. Replaced by (47284001, SCT, "Extra abdominal desmoid"). |
||
A cyst formed of a mass of epithelial cells, as a result of trauma has been pushed beneath the epidermis. The cyst is lined with squamous epithelium and contains concentric layers or keratin |
Retired. Replaced by (419670003, SCT, "Epidermal inclusion cyst"). |
||
Retired. Replaced by (37058002, SCT, "Foreign body (reaction)"). |
|||
Retired. Replaced by (42385006, SCT, "Galactocele"). |
|||
A congenital anomaly that leads to a proliferation of blood vessels leading to a mass that resembles a neoplasm, not located in parenchymal areas but subcutaneous |
Retired. Replaced by (93473009, SCT, "Hemangioma of subcutaneous tissue"). |
||
Retired. Replaced by (76197007, SCT, "Hyperplasia, usual"). |
|||
A form of fibrocystic disease in young woman with florid and sclerosing adenosis that microscopically may suggest carcinoma. |
|||
Enlarging masses during lactation. A circumscribed benign tumor composed primarily of glandular structures with scanty stroma, with prominent secretory changes in the duct |
Retired. Replaced by (128651002, SCT, "Lactating adenoma"). |
||
Solitary or multiple tumors of muscles and fibrous tissues, or tumors composed of myofibroblasts |
Retired. Replaced by (128738002, SCT, "Myofibroblastoma"). |
||
Irregular clusters of small tubules are present in adipose or fibrous tissue, resembling tubular carcinoma but lacking stromal fibroblastic proliferation. |
|||
Papilloma typically involving an aggregate of adjacent ducts in the periphery of the breast, likely representing involvement of several foci of one or two duct systems. |
|||
Condition in which there are tumors of various sizes on peripheral nerves. They may be neuromas or fibromas |
Retired. Replaced by (81669005, SCT, "Neurofibromatosis"). |
||
A cyst resulting from the loss of the epithelial lining of a sebaceous dermoid or lacteal cyst. |
|||
Breast tissue with characteristics of a benign nature, following breast reduction surgery. |
|||
A benign stromal lesion composed of intermixed stromal and epithelial elements. The lobular and duct structures of the breast parenchyma are separated by an increased amount of stroma, non specific proliferative epithelial changes include hyperplasia of duct and lobular epithelium often with accentuation of myoepithelial cells and aprocine metaplasia with or without cyst formation. |
|||
An nonencapsulated stellate lesion consisting of a fibroelastic core and radiating bands of fibrous connective tissue containing lobules manifesting adenosis and ducts with papillary or diffuse intraductal hyperplasia |
Retired. Replaced by (133855003, SCT, "Radial scar"). |
||
Retired. Replaced by (50916005, SCT, "Sclerosing adenosis"). |
|||
Nodular inflammatory lesions due to the presence of silicone in the breast tissue. |
|||
Spontaneous excessive proliferation of breast tissue, usually found in younger women. |
|||
A malignant neoplasm occurring most often in breast and skin, believed to originate from endothelial cells of blood vessels, microscopically composed of closely packed round or spindle shaped cells, some of which line small spaces resembling vascular clefts |
Retired. Replaced by (39000009, SCT, "Angiosarcoma"). |
||
Histological changes to the vascular system related to an invasive process. |
|||
Carcinoma of the breast found in patients less than 20 years of age. |
|||
A carcinoma found in supernumerary breasts and aberrant breast tissue. |
|||
A carcinoma that synthesizes substances, including hormones, not considered to be normal products of the breast. |
|||
A basal cell carcinoma that arises in the nipple of the breast. |
|||
Retired. Replaced by (22694002, SCT, "Carcinoma with metaplasia"). |
|||
Carcinoma of the breast presenting during pregnancy or lactation. |
|||
A malignant neoplasm that contains elements of carcinoma and sarcoma, so extensively intermixed as to indicate neoplasia of epithelial and mesenchymal tissue |
Retired. Replaced by (63264007, SCT, "Carcinosarcoma"). |
||
A non-invasive carcinoma restricted to the glandular lumen characterized by less aggressive malignant cytologic features and behavior. |
|||
Retired. Replaced by (128696009, SCT, "Intraductal carcinoma micro-papillary"). |
|||
A malignant neoplasm characterized by the formation of numerous, irregular, finger-like projections of fibrous stroma that is covered with a surface layer of neoplastic epithelial cells found in a cyst. |
|||
Carcinoma with both characteristics of localized and spreading disease. |
|||
Retired. Replaced by (89740008, SCT, "Invasive lobular carcinoma"). |
|||
Mammary infiltrates as a secondary manifestation in patients with established leukemia. |
|||
Histological changes to the lymphatic system related to an invasive process. |
|||
A heterogeneous group of neoplasms arising in the reticuloendoethelial and lymphatic systems |
Retired. Replaced by (1163043007, SCT, "Lymphoma"). |
||
Occult carcinoma presenting with axillary lymph node metastases |
A small carcinoma, either asymptomatic or giving rise to metastases without symptoms due to the primary carcinoma presenting with metastatic disease in the axillary lymph nodes. |
||
A malignant lesion in the breast with morphologic patterns not typical of breast carcinoma arising from a non-mammary malignant neoplasm. |
|||
A malignant lesion in the breast with morphologic patterns not typical of breast carcinoma arising from a neoplasm in the colon. |
|||
A malignant lesion in the breast with morphologic patterns not typical of breast carcinoma arising from a neoplasm in the lung. |
|||
A malignant lesion in the breast with morphologic patterns not typical of breast carcinoma arising from a melanoma. |
|||
A malignant lesion in the breast with morphologic patterns not typical of breast carcinoma arising from a neoplasm in the ovary. |
|||
A malignant lesion in the breast with morphologic patterns not typical of breast carcinoma arising from a sarcoma. |
|||
Multiple foci of non-invasive carcinoma restricted to the glandular lumen. |
|||
A malignant lesion in an axillary node arising from a non-axillary neoplasm. |
|||
Retired. Replaced by (34360000, SCT, "Malignant fibrous histiocytoma"). |
|||
A malignant lesion in a intramammary lymph node arising from a non-intramammary lymph node neoplasm. |
|||
A malignant melanoma of the skin that arises in the nipple of the breast. |
|||
Retired. Replaced by (126510002, SCT, "Neoplasm of the mammary skin"). |
|||
Retired. Replaced by (10376009, SCT, "Papillary carcinoma in-situ"). |
|||
Squamous cell carcinoma to the terminal portion of the alveolar. |
|||
A non-invasive carcinoma restricted to the glandular lumen characterized by more aggressive malignant cytologic features and behavior. |
|||
Retired. Replaced by (30156004, SCT, "Invasive cribriform carcinoma"). |
|||
An indication that some or all of the margin of a lesion has sharp corners, often forming acute angles. |
|||
Calcifications that vary in sizes and shapes and are usually smaller than0.5 mm in diameter. |
|||
An indicator that calcifications are imbedded within a mass. |
|||
An indicator that calcifications are imaged outside of a mass finding. |
|||
Fat lobules and uniformly echogenic bands of supporting structures comprise the bulk of breast tissue. |
|||
A uniformly echogenic layer of fibroglandular tissue is seen beneath a thin layer of subcutaneous fat. |
|||
The breast texture is characterized by multiple small areas of increased and decreased echogenicity. |
|||
Referential relationship of the finding to the imaging device as noted on sonography. |
|||
The long axis of a lesion parallels the skin line ("wider-than-tall" or in a horizontal orientation). |
|||
The anterior-posterior or vertical dimension is greater than the transverse or horizontal dimension. |
|||
The lesion boundary describes the transition zone between the mass and the surrounding tissue. |
|||
The sharp demarcation between the lesion and surrounding tissue can be imperceptible or a distinct well-defined echogenic rim of any thickness. |
|||
There is no sharp demarcation between the mass and the surrounding tissue, which is bridged by an echogenic transition zone. |
|||
An imaging characteristic of resonance noted during sonography. |
|||
Having increased echogenicity relative to fat or equal to fibroglandular tissue. |
|||
Defined relative to fat; masses are characterized by low-level echoes throughout. E.g., appearance of a complicated cyst or fibroadenoma. |
|||
Having the same echogenicity as fat (a complicated cyst or fibroadenoma may be isoechoic or hypoechoic). |
|||
The attenuation characteristics of a mass with respect to its acoustic transmission. |
|||
More than one pattern of posterior attenuation, both shadowing and enhancement. |
|||
Sonographic appearance of adjacent structures relative to a mass finding. |
|||
Vascularity on imaging is seen immediately adjacent to a lesion. |
|||
Vascularity on imaging is considered diffusely elevated within the surrounding breast tissue. |
|||
Relationship of the new anomaly to other clinical or imaging anomalies. |
|||
An indication that the current imaging finding relates to a finding from a clinical breast examination. |
|||
An indication that the current imaging finding relates to a finding from a mammography study. |
|||
An indication that the current imaging finding relates to a finding from a breast MRI study. |
|||
An indication that the current imaging finding relates to a finding from a breast ultrasound study. |
|||
An indication that the current imaging finding relates to a finding from an imaging study. |
|||
An indication that the current imaging finding has no relation to findings from any other imaging study. |
|||
An indication that the current imaging finding has no relation to any other clinical findings. |
|||
A breast cancer with malignant pathology findings that are not classified as invasive or in situ. |
|||
In the first week of the menstrual cycle phase, that is, one week following menses. |
|||
In the second week of the menstrual cycle phase, that is, two weeks following menses. |
|||
In the third week of the menstrual cycle phase, that is, three weeks following menses. |
|||
Report title for the diagnostic report for one or more breast imaging or intervention procedures. |
|||
Concept name for the description of why a procedure has been performed. |
Retired. Replaced by (18785-6, LN, "Indications for Procedure"). |
||
A finding during clinical examination (i.e., history and physical examination) such as pain, palpable mass or discharge. |
|||
First screening mammogram taken for patient that is used as a comparison baseline for further examinations. |
|||
First mammogram taken for a patient without regard to whether it was for screening or a diagnostic procedure. |
|||
Concept name for the material of which a breast prosthetic device is constructed. |
|||
A numeric count of findings classified as similar in nature. |
|||
Concept name for the status of a breast prosthetic device as noted by imaging. |
|||
Replaced by (46342-2, LN, "breast ffd mammogram"). |
|||
Computer aided detection and/or computer aided diagnosis for mammography. |
|||
A title for a report section that summarizes all interpretation results for a report with one overriding assessment. E.g., benign or negative. |
|||
Concept name for a collection of supporting evidence for a report. |
|||
Prior study indicates that additional imaging be performed to further evaluate a suspicious or questionable anatomic region. |
|||
The prior study recommended a follow-up breast imaging study in 1 to 11 months (generally in 6 months). |
|||
Prior breast augmentation (breast enlargement) and is not presenting with any symptoms. |
|||
Review or second opinion made on an image performed outside of the facility. |
|||
Additional evaluation requested from abnormal screening study |
Additional breast imaging performed at the time of the patient's screening mammogram. |
||
Personal history of breast cancer with breast conservation therapy |
Patient has had a prior surgery such as a lumpectomy or quadrantectomy to remove malignant breast tissue, but breast tissue remains. |
||
The results of a physical examination performed on the patient, possibly including the results of inspection, palpation, auscultation, or percussion. |
|||
The result of assessing the current imaging study in comparison to previous imaging studies. |
|||
An abnormality observed during ductography where the ductal system within the breast fills in an abnormal pattern. Ductography is an imaging study in which a radio opaque contrast media is introduced into the ductal system of the breast through the nipple and images of the ductal system are obtained. |
|||
During ductography an observation of more than one filling abnormality within the breast ductal system. |
|||
An abnormality observed during ductography where the ductal system within the breast terminates in an unusual fashion. |
|||
Abnormal flowage of contrast media within the breast noted on ductography. |
|||
An abnormality observed during ductography where the ductal system within the breast appears narrow. |
|||
During ductography an observation of the contrast media filling a cyst within the breast. |
|||
The area and line within the anatomy through which a needle or instrument passes during an interventional procedure. |
|||
The line within the anatomy from the lower outer to the upper inner aspect. E.g., through which a needle or instrument passes in an interventional procedure. |
|||
The line within the anatomy from the lower inner to the upper outer aspect. E.g., through which a needle or instrument passes in an interventional procedure. |
|||
The line within the anatomy from the upper outer to the lower inner aspect. E.g., through which a needle or instrument passes in an interventional procedure. |
|||
The line within the anatomy from the upper inner to the lower outer aspect. E.g., through which a needle or instrument passes in an interventional procedure. |
|||
The number of times a biopsy instrument is passed through an area of interest. |
|||
The number of biopsy specimens obtained from an interventional procedure. |
|||
An indicator of whether or not a biopsy or localizing needle in an interventional procedure is seen to be in the area of interest. |
|||
The number of localizing needles placed around the area of interest in an interventional procedure. |
|||
An indicator of whether or not an incision was made in the anatomy during an interventional procedure. |
|||
An indicator of whether or not a radio opaque microclip was placed in the anatomy during an interventional procedure. |
Retired. Replaced by (111123, DCM, "Marker placement") |
||
An indicator of the degree of success of an interventional procedure. |
|||
An indicator that during an interventional procedure the area of interest was fully excised and is noted in the resultant biopsy specimen. |
|||
An indicator that during an interventional procedure the area of interest was partially excised and is noted in the resultant biopsy specimen. |
|||
An indicator that following an interventional procedure the area of interest is not seen in the resultant biopsy specimen. |
|||
An indicator that following an interventional procedure the targeted calcifications are noted in the resultant biopsy specimen. |
|||
An indicator that during an interventional procedure the area of interest was fully excised and is noted in the resultant biopsy specimen. |
|||
An indicator that during an interventional procedure the area of interest was partially excised and is noted in the resultant biopsy specimen. |
|||
An indicator that during an interventional procedure fluid was successfully aspirated. |
|||
An indicator of whether or not the fluid obtained during an interventional procedure contains red blood cells. |
|||
An indicator of whether or not fluid during an interventional procedure was sent for cytological analysis or simply discarded. |
|||
An indicator that fluid obtained during an interventional procedure was sent to a laboratory for analysis. |
|||
An indicator that fluid obtained during an interventional procedure was discarded. |
|||
A radiopaque density noted during diagnostic imaging that has associated calcific densities. |
|||
A fluid-filled sac with greater than normal characteristics. |
|||
Supporting evidence for interpretation results of an interventional procedure. |
|||
A descriptor that further qualifies or characterizes a type of procedure. |
|||
Needle size (diameter) characterization. E.g., of a biopsy needle. |
|||
An indicator of the gravity of a problem experienced by a patient, related to a procedure that was performed. |
|||
The collection of observations and findings from pathologic analysis. |
|||
The date and time that the sample was collected from the patient. |
|||
Indicates that the margin of the biopsy specimen was not involved with the tumor. |
|||
Indicates that the margin of the biopsy specimen was involved with the tumor. |
|||
Indicates whether the nipple was involved in an interventional procedure or pathologic analysis. |
|||
Indicates the number of lymph nodes removed that contain cancer cells. |
|||
The result of a test for the presence of a protein that binds with estrogen. |
|||
The result of a test for the presence of a protein that binds with progesterone. |
|||
Indicates the percentage of cells in S phase. Cell division is defined by phases; the S phase is the stage during which DNA replicates. |
|||
The inability to discern normal versus abnormal breast tissue during palpation. |
|||
An indication that a patient has or had a malignant occurrence in an area of the body other than the breast. |
|||
A salt water filled prosthetic device implanted in the breast. |
|||
A polymer based (plastic) prosthetic device implanted in the breast. |
|||
The introduction of polymeric organic silicon based material through the skin, as for breast augmentation or reconstruction. |
|||
A prosthetic device that contains more than one material implanted in the breast. |
|||
A breast implant placed in front of the pectoralis major muscle. |
|||
Using X-Ray technique and a superimposed set of crossed lines for detection or placement. |
|||
Using X-Ray technique and a superimposed aperture for detection or placement. |
|||
The performance of a biopsy procedure using a vacuum device attached to the biopsy needle. |
|||
Having experienced no adverse medical conditions related to or resulting from an interventional procedure. |
|||
TNM grouping of tumor stage, from AJCC, where primary tumor is Tis, regional lymph node is N0, and distant metastasis is M0. |
|||
TNM grouping of tumor stage, from AJCC, where primary tumor is T1, regional lymph node is N0, and distant metastasis is M0. |
|||
TNM grouping of tumor stage, from AJCC, where primary tumor is T0 or T1, with regional lymph node N1 and distant metastasis is M0, or T2 with N0 and M0. |
|||
TNM grouping of tumor stage, from AJCC, where primary tumor is T2, with regional lymph node N1 and distant metastasis is M0, or T3 with N0 and M0. |
|||
TNM grouping of tumor stage, from AJCC, where primary tumor is T0, T1 or T2, with regional lymph node N2 and distant metastasis is M0, or T3 with N1 or N2 and M0. |
|||
TNM grouping of tumor stage, from AJCC, where primary tumor is T4, regional lymph node is N0, N1 or N2, and distant metastasis is M0. |
|||
TNM grouping of tumor stage, from AJCC, where primary tumor is any T value, regional lymph node is N3, and distant metastasis is M0. |
|||
TNM grouping of tumor stage, from AJCC, where primary tumor is any T value, regional lymph node is any N value, and distant metastasis is M1. |
|||
Histologic tumor grade (sometimes called Scarff-Bloom-Richardson grade) is based on the arrangement of the cells in relation to each other -- whether they form tubules, how closely they resemble normal breast cells (nuclear grade) and how many of the cancer cells are in the process of dividing (mitotic count). |
|||
Breast prosthetic devices are intact, not leaking, and are in a normal shape and form. |
|||
Breast prosthetic devices are not symmetric, equal, corresponding in form, or are in one breast (unilateral). |
|||
Fibrous or calcific contracture of the tissue capsule that forms around a breast prosthetic device. |
|||
Breast prosthetic device is twisted out of normal shape or form. |
|||
Silicone from breast prosthetic device found in lymphatic tissue. |
|||
Silicone found in breast tissue outside of the prosthetic capsule or implant membrane. |
|||
Protrusion of part of the structure normally encapsulating the content of the breast prosthetic device. |
|||
Historical patient health information of interest to the breast health clinician. |
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Information regarding usage by the patient of certain medications, such as hormones. |
Retired. Replaced by (10160-0, LN, "History Of Medication Use") |
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Interventional or non-interventional procedures previously performed on the patient, such as breast biopsies. |
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Abnormal conditions experienced by the patient that serve as the reason for performing a procedure, such as a physical breast examination. |
Retired. Replaced by (11450-4, LN, "Problem List") |
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Personal, familial, and other health factors that may indicate an increase in the patient's chances of developing a health condition or disease, such as breast cancer. |
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A classification of a medicinal substance, such as hormonal contraceptive or antibiotic. |
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Historical patient health information for general purpose use. |
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The age of the patient at the time of her first full term pregnancy. |
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The age of the patient at the time she had her left ovary removed. |
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The age of the patient at the time she had her right ovary removed. |
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The age of a patient on the first occurrence of an event, such as the first use of a medication. |
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The age of a patient on the last occurrence of an event, such as the last use of a medication. |
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The date and time of the first occurrence of an event, such as the first use of a medication. |
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The date and time of the last occurrence of an event, such as the last use of a medication. |
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An indicator of whether an event is still in progress, such as the use of a medication or substance, or environmental exposure. |
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Product name of a device or substance, such as medication, to identify it as the product of a single firm or manufacturer. |
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A descriptor that further qualifies or characterizes a risk factor. |
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A prior non-interventional study or interventional procedure performed on a patient. |
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Retired. Replaced by (364320009, SCT, "Pregnancy observable"). |
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A symptom experienced by a patient that is used as the reason for performing a study or procedure. |
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The function of the individual who is reporting information on a patient, which could be a specific health care related profession, the patient him/herself, or a relative or friend. |
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The date and time of the most recent evaluation of an indicated problem. |
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A patient's biological relative who exhibits a health factor that may indicate an increase in the patient's chances of developing a particular disease or medical problem. |
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The age at which an individual experienced a specific event, such as breast cancer. |
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The current stage of an individual in her gynecological development. |
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A gynecological hormone for which the specific type is not specified. E.g., contraceptive, estrogen, Tamoxifen. |
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An indicator of whether or not a patient ever provided breast milk to her offspring. |
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The average length of time that a patient provided breast milk to her offspring. |
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Information regarding usage by the patient of certain legal or illicit substances. |
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A classification of a substance, such as alcohol or a legal or illicit drug. |
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Information regarding exposure of the patient to potentially harmful environmental factors. |
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A classification of a potentially harmful substance or gas in a subject's environment, such as asbestos, lead, or carcinogens. |
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Previous Structured Reports that could have relevant information for a current imaging service request. |
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An indication that a patient has had a previous malignancy of the breast. |
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Indicates a previous occurrence of cancer of the lining of the uterus. |
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Indicates a previous occurrence of cancer of the lining of the ovary. |
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Indicates a prior diagnosis of pre-cancerous cells or tissue removed for pathologic evaluation. |
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A female patient whose first child was born after the patient was 30 years old. |
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The first level genetic marker indicating risk for breast cancer. |
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The second level genetic marker indicating risk for breast cancer. |
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The third level genetic marker indicating risk for breast cancer. |
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A patient's biological aunt, grandmother, or female cousin was diagnosed with breast cancer. Definition from BI-RADS®. |
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A patient's biological mother or sister was diagnosed with breast cancer after they had gone through menopause. Definition from BI-RADS®. |
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A patient's biological mother or sister was diagnosed with breast cancer before they had gone through menopause, or more than one of the patient's first-degree relatives (biological mother or sister) were diagnosed with breast cancer after they had gone through menopause. Definition from BI-RADS®. |
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Previous diagnosis of a malignancy of the prostate gland in a biological relative. |
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The health record of a patient's biological relatives is not known. |
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The study of cells obtained from fluid emitted from the breast. |
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A developmental abnormality resulting in an abnormal shape of the uterus. |
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A naturally occurring premature expulsion from the uterus of the products of conception - the embryo or a nonviable fetus. |
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An ailment/abnormality or state of the female reproductive tract. |
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A surgical operation performed on any portion of the female reproductive tract. |
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Prior pregnancy with a low birth weight baby or a fetus with Intrauterine Growth Restriction or Retardation. |
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History of at least one prior pregnancy with fetal anatomic abnormality(s). |
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History of delivering a Rhesis Isoimmunization affected child(ren) or a child(ren) with another blood disorder. |
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History of at least one pregnancy that contained more than one fetus. E.g., twins, triplets, etc. |
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Current pregnancy, known or suspected malformations/syndromes |
At least one fetus of this pregnancy has an anatomic abnormality(s) that is known to exist, or a "marker" is present that suggests the abnormality(s) may be present. |
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Biological relatives have previously conceived a fetus with an anatomic abnormality(s). |
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A subjective descriptor for an elevated amount of exposure, use, or dosage, incurring high risk of adverse effects. |
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A subjective descriptor for a moderate amount of exposure, use, or dosage, incurring medium risk of adverse effects. |
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A subjective descriptor for a limited amount of exposure, use, or dosage, incurring low risk of adverse effects. |
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A measurement of the rate of occurrence of which a patient takes a certain medication. |
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The quantity per unit of time that a patient was or is being exposed to an environmental irritant. |
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The quantity per unit of time that a medication or substance was or is being used. |
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A qualitative descriptor for the amount of a medication that was or is being taken. |
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A qualitative descriptor for the amount of present or past exposure to an environmental irritant. |
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A qualitative descriptor for the amount of a medication or substance that was or is being used. |
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A qualitative descriptor for the frequency with which a medication was or is being taken. |
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A qualitative descriptor for the frequency of present or past exposure to an environmental irritant. |
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A qualitative descriptor for the frequency with which a medication or substance was or is being used. |
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Patient is not known to have been exposed to or used the substance or medication. |
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Patient returns for additional images to improve the quality of the most recent study. |
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Patient returns for additional images to clarify findings from the most recent study. |
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Patient returns for additional images to clarify symptoms or signs reported by the patient or a healthcare professional at the time of the most recent study. |
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Number of births with low birth weight or intrauterine growth restriction. |
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Filter that transmits green light while blocking the other colors, typically centered at 510-540 nm |
Retired. Replaced by (445465004, SCT, "Green optical filter") |
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Filter that transmits red light while blocking the other colors, typically centered at 630-680 nm |
Retired. Replaced by (445279009, SCT, "Red optical filter") |
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Filter that transmits blue while blocking the other colors, typically centered at 460-480 nm |
Retired. Replaced by (445084008, SCT, "Blue optical filter") |
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A filter of 560nm that is used for retinal imaging and can provide good contrast and good visibility of the retinal vasculature |
Retired. Replaced by (445340000, SCT, "Yellow-green optical filter") |
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A filter of 490nm that is used for retinal imaging because of excessive scattering of some retinal structures at very short wavelengths |
Retired. Replaced by (422915004, SCT, "Blue-green optical filter") |
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Filter that transmits the infrared spectrum, which is light that lies outside of the visible spectrum, with wavelengths longer than those of red light, while blocking visible light |
Retired. Replaced by (445169002, SCT, "Infrared optical filter") |
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A filter that reduces reflections from non-metallic surfaces such as glass or water by blocking light waves that are vibrating at selected angles to the filter. |
Retired. Replaced by (445391002, SCT, "Polarizing optical filter") |
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Joslin NM-1 is a 45 degree field focused centrally between the temporal margin of optic disc and the center of the macula: Center the camera on the papillomacular bundle midway between the temporal margin of the optic disc and the center of the macula. The horizontal centerline of the image should pass directly through the center of the disc. |
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Joslin NM-2 is a 45 degree field focused superior temporal to the optic disc: Center the camera laterally approximately one-half disc diameter temporal to the center of the macula. The lower edge of the field is tangent to a horizontal line passing through the upper edge of the optic disc. The image is taken temporal to the macula but includes more retinal nasal and superior to the macula than standard field 2. |
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Joslin NM-3 is a 45 degree field focused nasal to the optic disc: This field is nasal to the optic disc and may include part of the optic disc. The horizontal centerline of the image should pass tangent to the lower edge of the optic disc. |
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A slit reflected light microscope, which has the ability to form an image of the back scattered light from the eye in a sagittal plane. Scheimpflug cameras are able to achieve a wide depth of focus by employing the "Sheimpflug principle" where the lens and image planes are not parallel with each other. Rotating Sheimplug cameras are able to generate three-dimensional images and calculate measurements of the anterior chamber of the eye. |
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Calculated from values of entrance exposure in air, the X-Ray beam quality (half-value layer), and compressed breast thickness, is the energy deposited per unit mass of glandular tissue averaged over all the glandular tissue in the breast. |
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The average thickness of the body part examined when compressed, if compression has been applied during X-Ray exposure. |
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Thickness of Aluminum required to reduce the X-Ray output at the patient entrance surface by a factor of two. |
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An anti-scatter device based on radiation absorbing strips above the detector. E.g., in the patient support. |
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Exposure measurement in air at the reference point that does not include back scatter, according to MQCM 1999. |
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Average Glandular Dose to a single breast accumulated over multiple images. |
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Value of the control variable used to parametrize the Automatic Exposure Control (AEC) closed loop. E.g., "Water Value". |
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A processing algorithm used to reduce the effect of X-Ray scatter on image quality, similar to the use of a physical X-Ray anti-scatter grid. |
This does not include processing for removal of physical anti-scatter grid lines. |
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A physical X-Ray anti-scatter grid that does not move during exposure. |
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A physical X-Ray anti-scatter grid with radiation absorbing strips that are focused toward the focal spot, to eliminate grid cutoff. |
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A physical X-Ray anti-scatter grid that is designed to move during exposure, to eliminate the appearance of grid lines on the image. |
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A physical X-Ray anti-scatter grid with radiation absorbing strips that are parallel to each other and that is used only with long source to image distances. |
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A physical X-Ray anti-scatter grid with crossed radiation absorbing strips used for more complete cleanup of scatter radiation. |
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No physical X-Ray anti-scatter grid was used due to low scatter conditions. |
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The compression force applied to the body part during exposure. |
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The average compression pressure applied to the body part during exposure. |
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The area of the body part to which compression has been applied during exposure. |
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Refractive measurements of the eye to correct for inability to focus at near while wearing the distance prescription. |
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Refractive measurements of the eye to correct for inability to focus at intermediate distance while wearing the distance prescription. |
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Refractive measurements of the eye to correct for inability to focus at the specified distance while wearing the distance prescription. |
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The power of a prism to bend light in the horizontal direction, in prism diopters. |
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Direction of the base of a horizontal prism -- either in (toward the nose), or out (away from the nose). |
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The power of a prism to bend light in the vertical direction, in prism diopters. |
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Direction of the base of a vertical prism -- either up, or down. |
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Distance in mm between the pupils when the patient's object of regard is in the distance. |
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Distance in mm between the pupils when the patient's object of regard is at near. |
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Small Incision Lenticule Extraction. Refractive surgery procedure where a thin lenticule is cleaved from the corneal stroma using a femtosecond laser and then extracted through a small incision in the corneal periphery. |
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A patient's vision with the correction measured by an autorefractor in place. |
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A patient's vision with whichever vision correction the patient customarily wears. |
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A patient's vision with the final spectacle prescription in place. |
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A macular grid thickness and volume report for a patient. The macular grid is an analytic tool described in PS3.17. |
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A numeric rating of the quality of the entire analysis with respect to grading and diagnostic purposes. |
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A numeric rating of the quality of an entire image set with respect to grading and diagnostic purposes. |
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The assessment of the centricity and persistence of the visual fixation (direction of gaze) during the acquisition. |
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The reason why the patient's visual fixation was not steady or was indeterminate. |
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The reason why the macular grid measurements may be questionable. |
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Identifier of container (box, block, microscope slide, etc.) for the specimen under observation. |
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Description of the individual step in the tissue processing sequence. |
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Identifier of the parent specimen that gave rise to the current specimen. |
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Description of coordinate system and origin reference point on parent specimen, or parent specimen container, or image used for localizing the sampling site or location within container or image. |
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Reference to image of parent specimen localizing the sampling site; may include referenced Presentation State object. |
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Location of sampling site of specimen (nominal center) relative to the Position Frame of Reference. |
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Location of sampling site of specimen (nominal center) relative to the Position Frame of Reference. |
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Location of sampling site of specimen (nominal center) relative to the Position Frame of Reference. |
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Description of specimen location, either in absolute terms or relative to the Position Frame of Reference. |
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Location of specimen (nominal center) relative to the Position Frame of Reference in the X dimension. |
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Location of specimen (nominal center) relative to the Position Frame of Reference in the Y dimension. |
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Location of specimen (nominal center) relative to the Position Frame of Reference in the Z dimension. |
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Description of visual distinguishing identifiers. E.g., ink, or a particular shape of the specimen. |
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Dissection of specimen with submission of all its sections for further processing or examination. |
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Dissection of specimen with submission of representative sections for further processing or examination. |
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A workflow step, during which tissue specimens are stored in a climate-controlled environment. |
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Epifluorescence illumination method for specimen microscopy. |
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Differential interference contrast method for specimen microscopy. |
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Total internal reflection fluorescence method for specimen microscopy. |
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A method of obtaining ophthalmic axial measurements that uses ultrasound, and that requires applanation of the cornea. |
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A method of obtaining ophthalmic axial measurements that uses ultrasound, and that requires immersion of the patient's eye in fluid as he lies in a supine position. |
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A method of obtaining ophthalmic axial measurements that uses light. |
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Measurements taken of the corneal curvature using a manual keratometer. |
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Measurements taken of the corneal curvature using an automated keratometer. |
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Simulated Keratometry measurements derived from corneal topography. |
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Method of determining the total cornea power from measuring the curvature of both anterior and posterior surface of the cornea. |
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Method of measuring the curvature of posterior surface of the cornea and determining its refractive power. |
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The Haigis IOL calculation formula. Haigis W, Lege B, Miller N, Schneider B. Comparison of immersion ultrasound biometry and partial coherence interferometry for intraocular lens calculation according to Haigis. Graefes Arch Clin Exp Ophthalmol 2000;238:765-73. |
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The Haigis-L IOL calculation formula. Haigis W. Intraocular lens calculation after refractive surgery for myopia: Haigis-L formula. J Cataract Refract Surg. 2008 Oct;34(10):1658-63. |
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The Holladay 1 IOL calculation formula. Holladay JT, Prager TC, Chandler TY, Musgrove KH, Lewis JW, Ruiz RS. A three-part system for refining intraocular lens power calculations. J Cataract Refract Surg. 1988; 14:17-24. |
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The Hoffer Q IOL calculation formula. Hoffer KJ. The Hoffer Q formula: a comparison of theoretic and regression formulas. J Cataract Refract Surg 1993;19:700-12. Errata. J Cataract Refract Surg 1994;20:677 and 2007;33:2-3. |
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The Olsen IOL calculation formula. Olsen T. Calculation of intraocular lens power: a review. Acta Ophthalmol. Scand. 2007: 85: 472-485. |
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The SRKII IOL calculation formula. Sanders DR, Retzlaff J, Kraff MC. Comparison of the SRK II formula and other second generation formulas. J Cataract Refract Surg. 1988 Mar;14(2):136-41. |
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The SRK-T IOL calculation formula. Retzlaff JA, Sanders DR, Kraff MC. Development of the SRK/T intraocular lens implant power calculation formula. J Cataract Refract Surg 1990;16:333-40. Erratum 1990;16:528. |
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Anterior chamber depth defined as the front of the cornea to the front of the lens. |
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Anterior chamber depth defined as the back of the cornea to the front of the lens. |
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Refers to the anterior lens when there are two lenses in the eye. The distance, in mm, from the anterior surface of the lens to the posterior surface of the lens. |
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Refers to the posterior lens when there are two lenses in the eye. The distance, in mm, from the anterior surface of the lens to the posterior surface of the lens. |
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Value obtained from measurements taken by the device creating this SOP Instance. |
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Value obtained by data transfer from an external source - not from measurements taken by the device providing the value. |
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Standard Deviation is a simple measure of the variability of data. |
|||
Signal to Noise Ratio of the data samples taken to create a measurement. |
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Projection from 2D image pixels to 3D Cartesian coordinates based on a spherical mathematical model. |
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Mapping from 2D image pixels to 3D Cartesian coordinates based on measurements of the retinal surface. E.g., of the retina, derived via a measurement technology such as Optical Coherence Tomography, Ultrasound etc. |
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Test pattern, nominally covering an area within 24° of fixation. Consists of 54 test points a minimum of 3° from each meridian and placed 6° apart. The "-2" distinguishes this from another 24° pattern (no longer supported). |
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Test pattern, nominally covering an area within 10° of fixation. Consists of 68 test points a minimum of 1° from each meridian and placed 2° apart. The "-2" in this case indicates its point layout to be similar to the 30-2 and 24-2. |
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Test pattern consisting of test point locations within 30° of fixation. Consists of 76 test points a minimum of 3° from each meridian and placed 6° apart. The "-2" distinguishes this from another 30° pattern (no longer supported). |
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Test pattern consisting of 60 test point locations between 30° and 60° of fixation a minimum of 6° from each meridian and placed 12° apart. The "-4" distinguishes this from a similar 60° pattern having 4 additional points. |
|||
Test pattern consisting of 16 test point locations within 10° of fixation a minimum of 1° from each meridian and placed 2° apart. |
|||
Test pattern consisting of 40 test point locations within 30° of fixation that spread out radially from fixation. |
|||
Test pattern consisting of 76 test point locations within 30° of fixation a minimum of 3° from each meridian and placed 6° apart. |
|||
Test pattern consisting of 60 test point locations between 30° and 60° of fixation a minimum of 6° from each meridian and placed 12° apart. |
|||
Test pattern consisting of 81 test point locations within 60° of fixation that spread out radially from fixation. |
|||
Test pattern consisting of 120 test point locations within 60° of fixation that spread out radially from fixation, concentrated in the nasal hemisphere. |
|||
Test pattern for Glaucoma and general visual field assessment with 59 test locations of which 16 test locations are in the macular area (up to 10° eccentricity) and where the density of test location is reduced with eccentricity. The test can be extended with the inclusion of 14 test locations between 30° and 60° eccentricity, 6 of which are located at the nasal step. |
|||
Test pattern for the macular area. Orthogonal test pattern with 0.7° spacing within the central 4° of eccentricity and reduced density of test locations between 4 and 10, 5° of eccentricity. 81 test locations over all. The test can be extended to include the test locations of the Visual Field G Test Pattern between 10, 5° and 60°. |
|||
Full field test pattern with 48 test locations from 0-30° and 82 test locations from 30-70°. Reduced test point density with increased eccentricity. Can be combined with screening and threshold strategies. |
|||
Low Vision Central. Orthogonal off-center test pattern with 6° spacing. 75 test locations within the central 30°. Corresponds with the 32/30-2 excluding the 2 locations at the blind spot, including a macular test location. The LVC is linked with a staircase threshold strategy starting at 0 dB intensity and applies stimulus area V. |
|||
General test corresponding to the 30-2 but excluding the 2 test locations in the blind spot area, hence with 74 instead of 76 test locations. |
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Swedish Interactive Thresholding Algorithm (SITA). Strategy gains testing efficiency through use of visual field and information theory models. In: Bengtsson B, Olsson J, Heijl A, Rootzen H. A new generation of algorithms for computerized threshold perimetry, SITA. Acta Ophthalmologica Scandinavica, 1997, 75: 368-375. |
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Similar to SITA-Standard but with less strict criteria for closing test points. Intended for patients who must be tested in the shortest possible time. In: Bengtsson B, Hejl A. SITA Fast, a new rapid perimetric threshold test. Description of methods and evaluation in patients with manifest and suspect glaucoma. Acta Ophthalmologica Scandinavica, 1998, 76: 431-437. |
|||
Threshold test algorithm that determines a patient's sensitivity at each test point in the threshold test pattern by adjusting intensity by 4 dB steps until the patient changes their response, and then adjusts the intensity in the opposite direction by 2 dB steps until the patient changes their response again. The last stimulus seen by the patient is recognized as the threshold for that point. The starting values are determined by first thresholding a "primary" point in each quadrant then using the results of each primary point to determine the starting values for neighboring points. |
|||
Similar to the Full Threshold algorithm except that it steps by 3 dB and only crosses the threshold only once. In: Flanagan JG, Wild JM, Trope GE. Evaluation of FASTPAC, a new strategy for threshold estimation with the Humphrey Field Analyzer, in a glaucomatous population. Ophthalmology, 1993, 100: 949-954. |
|||
Identical to Full Threshold except that starting values are determined by the results of a previous test performed using the same test pattern and the Full Threshold test strategy. |
|||
Similar to FastPac except that the steps are pseudo-dynamic (differ based on the intensity of the last presentation). |
|||
Suprathreshold testing strategy, in which each point is initially tested using stimulus that is 6 dB brighter than the expected hill of vision. If the patient does not respond, the stimulus is presented a second time at the same brightness. If the patient sees either presentation, the point is marked as "seen"; otherwise it is marked as "not seen". |
|||
An extension of the two-zone strategy in which test points where the second stimulus is not seen are presented with a third stimulus at maximum brightness. |
|||
An extension of the two-zone strategy, in which test points where the second stimulus is not seen receive threshold testing to quantify the depth of any detected scotomas. |
|||
Tendency Oriented Perimetry. Fast thresholding algorithm. Test strategy makes use of the interaction between neighboring test locations to reduce the test time compared to normal full threshold strategy by 60-80%. In: Morales J, Weitzman ML, Gonzalez de la Rosa M. Comparison between Tendency-Oriented Perimetry (TOP) and octopus threshold perimetry. Ophthalmology, 2000, 107: 134-142. |
|||
Dynamic strategy is a fast thresholding strategy reducing test duration by adapting the dB step sizes according to the frequency-of-seeing curve of the threshold. Reduction of test time compared to normal full threshold strategy 30-50%. |
|||
Traditional full threshold staircase strategy. Initial intensities are presented, based on anchor point sensitivities in each quadrant and based on already known neighboring sensitivities. In a first run, thresholds are changed in 4dB steps until the first response reversal. Then the threshold is changed in 2 dB steps until the second response reversal. The threshold is calculated as the average between the last seen and last not-seen stimulus, supposed to correspond with the 50% point in the frequency-of-seeing curve. |
|||
One level screening test: Each test location is tested with a single intensity. The result is shown as seen or not-seen. The intensity can either be a 0 dB stimulus or a predefined intensity. |
|||
Two level screening test: Each test location is initially tested 6 dB brighter than the age corrected normal value. |
|||
Low Vision Strategy is a full threshold normal strategy with the exception that it starts at 0 dB intensity and applies stimulus area V. |
|||
German Adaptive Threshold Estimation is a fast strategy based on a modified 4-2 staircase algorithm, using prior visual fields to calculate the starting intensity. In: Chiefer U, Pascual JP, Edmunds B, Feudner E, Hoffmann EM, Johnson CA, Lagreze WA, Pfeiffer N, Sample PA, Staubach F, Weleber RG, Vonthein R, Krapp E, Paetzold J. Comparison of the new perimetric GATE strategy with conventional full-threshold and SITA standard strategies. Investigative Ophthalmology and Visual Science, 2009, 51: 488-494. |
|||
Similar to GATE. The i stands for initial. If there was no prior visual field test to calculate the starting values, an anchor point method is used to define the local start values. |
|||
A test started as two level screening test. In the course of the test, the threshold of relative defects and/or normal test locations has been quantified using the dynamic threshold strategy. |
|||
A test started as two level screening test. In the course of the test, the threshold of relative defects and/or normal test locations has been quantified using the normal full threshold strategy. |
|||
Takes neighborhood test point results into account and offers stimuli with an adapted value to save time. |
|||
Continuous Luminance Incremental Perimetry, which measures at first the individual reaction time of the patient and threshold values in every quadrant. The starting value for the main test is slightly below in individual threshold. |
|||
A supra threshold screening strategy. The starting stimuli intensities depend on the classification of the patient's visual hill by measuring the central (fovea) or peripheral (15° meridian) threshold. The result of each dot slightly underestimates the sensitivity value (within 5 dB). |
|||
Mode for determining the starting luminance for screening test points - the starting luminance s is chosen based on the age of the patient. |
|||
Mode for determining the starting luminance for screening test points - the starting luminance is chosen based on the results of thresholding a set of "primary" test points (one in each quadrant). |
|||
Mode for determining the starting luminance for screening test points - in this case, all starting luminance is set to the same value. |
|||
Mode for determining the starting luminance for screening test points - the starting luminance is chosen based on the result of the foveal threshold value. |
|||
Mode for determining the starting luminance for screening test points - the starting luminance is chosen based on the result of four threshold values measured near the 15° meridian (one in each quadrant). |
|||
Real time evaluation of the camera image to recognize blinks and fixation losses with influence on the test procedure. Blinks that interfere with stimuli presentation cause the automated repetition of such stimulus presentations. Fixation losses can be used to delay the stimulus presentation until correct fixation is regained. |
|||
A method of monitoring the patient's fixation by periodically presenting stimulus in a location on the background surface that corresponds to the patient's blind spot. |
|||
A method of monitoring the patient's fixation by presenting the stimulus to the patient's macula. |
|||
A method of monitoring the patient's fixation by observation from the examiner of the patient. |
|||
Analysis Results identify Borderline and general reduction in sensitivity. |
|||
Index of a patient's remaining visual field normalized for both age and generalized defect. |
|||
Estimate of the portion of a patient's visual field loss that is diffuse (i.e., spread evenly across all portions of the visual field). |
|||
Estimate of the portion of a patient's visual field loss that is local (i.e., not spread evenly across all portions of the visual field). |
|||
An analysis of asymmetry between zones of the superior and inferior visual field. It is designed to be specific for defects due to glaucoma. |
|||
The data output of an optical fixation monitoring process, consisting of a list of positive and negative numbers indicating the quality of patient fixation over the course of a visual field test. The value 0 represents the initial fixation. Negative numbers indicate a measuring error (i.e., the patient blinked). Positive numbers quantify the degree of eccentricity from initial fixation. |
|||
The Haigis Toric IOL calculation formula. Haigis, Wolfgang. Toric Iol Power Calculation. 2014. http://www.semanticscholar.org/paper/Toric-Iol-Power-Calculation-Haigis/033838182a57a1d2948ac7d3b115855e29d03fad |
|||
The Haigis-L Toric IOL calculation formula. Haigis W, Intraocular lens calculation after refractive surgery for myopia: Haigis-L formula. J Cataract Refract Surg, 2008. 34(10): 1658-63. doi:10.1016/j.jcrs.2008.06.029 |
|||
The Barrett Toric IOL calculation formula. Abulafia, A., et al., Prediction of refractive outcomes with toric intraocular lens implantation. J Cataract Refract Surg, 2015. 41(5): p. 936-44. doi:10.1016/j.jcrs.2014.08.036 |
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The Barrett True-K IOL calculation formula. Abulafia, A., et al., Accuracy of the Barrett True-K formula for intraocular lens power prediction after laser in situ keratomileusis or photorefractive keratectomy for myopia. J Cataract Refract Surg, 2016. 42(3): p. 363-9. doi:10.1016/j.jcrs.2015.11.039 |
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The Barrett True-K Toric IOL calculation formula. Barrett G.D., Barrett True-K toric calculator. http://www.apacrs.org/TrueKToric105/TrueKToric.aspx |
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The Barrett Universal II IOL calculation formula. Barrett, G.D., An improved universal theoretical formula for intraocular lens power prediction. J Cataract Refract Surg, 1993. 19: p. 713-720. doi:10.1016/S0886-3350(13)80339-2 |
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The "Barrett Design Factor" constant used in IOL calculation. |
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An image of at least 15° angular subtend that is centered on the macula; see Section U.1.8 “Relative Image Position Definitions” in PS3.17 . |
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An image of at least 15° angular subtend that is centered on the optic disc; see Section U.1.8 “Relative Image Position Definitions” in PS3.17 . |
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An image of any angular subtend that is centered on a lesion located in any region of the fundus; see Section U.1.8 “Relative Image Position Definitions” in PS3.17 . |
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An image of at least 15° angular subtend centered midway between the disc and macula and containing at least a portion of the disc and both the disc and the macula; see Section U.1.8 “Relative Image Position Definitions” in PS3.17 . |
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An image of at least 15° angular subtend positioned between the central zone and the equator, and spanning both the superior-temporal and superior-nasal quadrants of the fundus; see Section U.1.8 “Relative Image Position Definitions” in PS3.17 . |
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An image of at least 15° angular subtend positioned between the central zone and the equator in the superior-temporal quadrant of the fundus; see Section U.1.8 “Relative Image Position Definitions” in PS3.17 . |
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An image of at least 15° angular subtend positioned between the central zone and the equator, and spanning both the superior-temporal and inferior-temporal quadrants of the fundus; see Section U.1.8 “Relative Image Position Definitions” in PS3.17 . |
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An image of at least 15° angular subtend positioned between the central zone and the equator in the inferior-temporal quadrant of the fundus; see Section U.1.8 “Relative Image Position Definitions” in PS3.17 . |
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An image of at least 15° angular subtend positioned between the central zone and the equator, and spanning both the inferior-temporal and inferior-nasal quadrants of the fundus; see Section U.1.8 “Relative Image Position Definitions” in PS3.17 . |
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An image of at least 15° angular subtend positioned between the central zone and the equator in the inferior-nasal quadrant of the fundus; see Section U.1.8 “Relative Image Position Definitions” in PS3.17 . |
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An image of at least 15° angular subtend positioned between the central zone and the equator, and spanning both the superior-nasal and inferior-nasal quadrants of the fundus; see Section U.1.8 “Relative Image Position Definitions” in PS3.17 . |
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An image of at least 15° angular subtend positioned between the central zone and the equator in the superior-nasal quadrant of the fundus; see Section U.1.8 “Relative Image Position Definitions” in PS3.17 . |
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An image of at least 15° angular subtend positioned between the equator and the ora serrata, and spanning both the superior temporal and superior nasal quadrants of the fundus; see Section U.1.8 “Relative Image Position Definitions” in PS3.17 . |
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An image of at least 15° angular subtend positioned between the equator and ora serrata in the superior-temporal quadrant of the fundus; see Section U.1.8 “Relative Image Position Definitions” in PS3.17 . |
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An image of at least 15° angular subtend positioned between the equator and ora serrata, and spanning both the superior-temporal and inferior-temporal quadrants of the fundus; see Section U.1.8 “Relative Image Position Definitions” in PS3.17 . |
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An image of at least 15° angular subtend positioned between the equator and ora serrata in the inferior-temporal quadrant of the fundus; see Section U.1.8 “Relative Image Position Definitions” in PS3.17 . |
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An image of at least 15° angular subtend positioned between the equator and ora serrata, and spanning both the inferior-temporal and inferior-nasal quadrants of the fundus; see Section U.1.8 “Relative Image Position Definitions” in PS3.17 . |
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An image of at least 15° angular subtend positioned between the equator and ora serrata in the inferior-nasal quadrant of the fundus; see Section U.1.8 “Relative Image Position Definitions” in PS3.17 . |
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An image of at least 15° angular subtend positioned between the equator and ora serrata, and spanning both the superior-nasal and inferior-nasal quadrants of the fundus; see Section U.1.8 “Relative Image Position Definitions” in PS3.17 . |
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An image of at least 15° angular subtend positioned between the equator and ora serrata in the superior-nasal quadrant of the fundus; see Section U.1.8 “Relative Image Position Definitions” in PS3.17 . |
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Identifies the use of physical signals with respect to time to capture information. |
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Identifies the use of physical signals with respect to multiple frequencies to capture information. |
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Algorithm to compensate for variability in corneal birefringence. |
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Measurement of the retinal surface contour relative to an assigned datum plane. |
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Measurement approximating the distance related to the structure between the internal limiting membrane (ILM) and the outer boarder of the retinal nerve fiber layer (RNFL); see Section III.6 “Retinal Thickness Definition” in PS3.17 . |
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Measurement approximating the distance related to the structure between the ILM and the outer border of the inner plexiform layer (IPL), called the ganglion cell complex (GCC); see Section III.6 “Retinal Thickness Definition” in PS3.17 . |
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Measurement approximating the distance related to the structure between the ILM and the inner-outer segment junction (IS-OS); see Section III.6 “Retinal Thickness Definition” in PS3.17 . |
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Measurement approximating the distance related to the structure between the ILM and the retinal pigment epithelium (RPE); see Section III.6 “Retinal Thickness Definition” in PS3.17 . |
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Measurement approximating the distance related to the structure between the ILM and the Bruch's membrane (BM); see Section III.6 “Retinal Thickness Definition” in PS3.17 . |
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Thickness of a component of the posterior segment of the eye. E.g., thickness of retina, choroid, etc. |
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Ophthalmic Thickness map based upon statistical significance category (such as percentile) from normative data. |
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Ophthalmic Thickness map based upon deviation (such as microns) from normative data. |
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Ophthalmic Thickness Map related to another Ophthalmic Thickness Map or another SOP Instance. |
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An anatomic point centered midway between the disc and fovea centralis. |
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Assuming the null hypothesis is true, the conditional percent probability of observing this result is not statistically significant. |
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Assuming the null hypothesis is true, the conditional percent probability of observing this result is statistically significant, 95% unlikely to happen by chance. |
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Assuming the null hypothesis is true, the conditional percent probability of observing this result is statistically significant, 98% unlikely to happen by chance. |
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Assuming the null hypothesis is true, the conditional percent probability of observing this result is statistically significant, 99% unlikely to happen by chance. |
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Assuming the null hypothesis is true, the conditional percent probability of observing this result is statistically significant, 99.5% unlikely to happen by chance. |
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A two dimensional representation of the axial curvature of the cornea. Axial curvature is calculated from the reciprocal of the distance from a point on a meridian normal at the point to the corneal topographer axis. Also known as sagittal curvature. |
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A two dimensional representation of the instantaneous curvature of the cornea. Instantaneous curvature is calculated from the reciprocal of the distance from a point on a meridian normal at the point to the center of curvature of that point. Also called tangential curvature. |
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A two dimensional representation of the refractive power of the cornea. Corneal refractive power is calculated using Snell's Law. |
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A two dimensional representation of the elevation of the cornea. Elevation is calculated as the distance from a point on the corneal surface to a point on a reference surface along a line parallel to the corneal topographer axis. For the purpose of visualization the reference surface is usually a sphere or an ellipse. |
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A two dimensional representation of a wavefront aberration surface of the cornea. Wavefront aberration surface is calculated from the corneal elevation data fit with either the Zernike polynomial series or the Fourier Series. Maps generally display total aberrations and selectable higher order aberrations. |
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A device that measures corneal anterior surface shape using elevation-based methods (stereographic and light slit-based). Rasterstereography images a grid pattern illuminating the fluorescein dyed tear film with 2 cameras to produce 3D. Slit-based devices scan the cornea, usually by rotation about the instrument axis centered on the cornea vertex. |
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A reflection-based device that projects a pattern of light onto the cornea and an image of the reflection of that pattern from the tear film is recorded in one video frame. Light patterns include the circular mire pattern (Placido disc) and spot matrix patterns. Sequential scanning of light spots reflected from the corneal surface is also used requiring multiple video frames for recording. |
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An Interference-based device that projects a beam of light onto and through the cornea. Light reflected from within the cornea is combined with a reference beam giving rise to an interference pattern. Appropriately scanned, this imaging is used to construct 3-dimensional images of the cornea from anterior to posterior surfaces. E.g., swept source OCT. |
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A structured report containing the results of computer-aided detection or diagnosis applied to chest imaging and associated clinical information. |
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The shadow of an absorber that attenuates the X-Ray beam more effectively than do surrounding absorbers. In a radiograph, any circumscribed area that appears more nearly white (of lesser photometric density) than its surround [Fraser and Pare]. |
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A collection of opacities detected within the continuum of loose connective tissue throughout the lung, that is not expected in a diagnostically normal radiograph. |
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A type of anatomy that is expected to be detectable on a radiographic (X-Ray based) image. |
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Characteristic of the extent of spreading of a finding or feature. |
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Characteristic of the clarity of the boundary or edges of a finding or feature. |
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The part(s) of the anatomy affected or encompassed by a finding or feature. |
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Characteristic of the matter or substance within a finding or feature. |
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Characteristic of the surface or consistency of a finding or feature. |
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Position of the X-Ray beam about the patient from the RAO to LAO direction where movement from RAO to vertical is positive. |
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Position of the X-Ray beam about the patient from the caudal to cranial direction where movement from caudal to vertical is positive. |
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The zone, lobe or segment within the chest cavity in which a finding or feature is situated. |
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Vertical refers to orientation parallel to the superior-inferior (cephalad-caudad) axis of the body, with horizontal being perpendicular to this, and an oblique orientation having projections in both the horizontal and vertical. |
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Characteristic of the shape formed by the boundary or edges of a finding or feature. |
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Indicates whether a finding was considered a target lesion, non-target lesion, or non-lesion during evaluation of a baseline series, according to a method such as RECIST. |
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The extent of a detected cavity, represented as the percent of the surrounding volume that it occupies. |
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The extent of a detected calcification, represented as the percent of the surrounding surface that it occupies. |
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The extent of a detected calcification, represented as the percent of the surrounding volume that it occupies. |
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A heading for the reporting of response evaluation for treatment of solid tumors. |
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The system applied in the reporting of response evaluation for treatment of solid tumors. |
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Response Evaluation Criteria In Solid Tumors; see Normative References. |
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A term that further specifies the name of an item that is an inferred correlation relating two or more individual findings or features. |
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A term that further specifies the name of an item that was detected on one image. |
|||
A qualitative descriptor for the extent of a finding or feature. |
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A qualitative descriptor for the thickness of tubular structures, such as blood vessels. |
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A characteristic that further describes the nature of an opacity. |
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The type of adverse affect that a finding or feature is having on the surrounding anatomy. |
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Response evaluation method as defined in chapter 5, "Reporting of Response" of the WHO Handbook for Reporting Results for Cancer Treatment; see Normative References. |
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Identification of the morphology of detected calcifications. |
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A quantitative numerical statement of the relative attenuation of the X-Ray beam at a specified point. Coefficient that describes the fraction of a beam of X-Rays or gamma rays that is absorbed or scattered per unit thickness of the absorber. This value basically accounts for the number of atoms in a cubic cm volume of material and the probability of a photon being scattered or absorbed from the nucleus or an electron of one of these atoms. Usually expressed in Hounsfield units [referred to as CT Number in Fraser and Pare]. |
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An X-Ray attenuation coefficient that is used as a threshold. E.g., in calcium scoring. |
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An opacity that is not expected in a diagnostically normal radiograph. |
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A textual description of the mathematical method of calculation that resulted in a calculated value. |
|||
American College of Radiology. ACR Standard for the Performance of Pediatric and Adult Chest Radiography. In: Standards. Reston, Va: 2001:95-98. |
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American College of Radiology. ACR Position Statement for Quality Control and Improvement, Safety, Infection Control, and Patient Concerns. In: Practice Guidelines and Technical Standards. Reston, Va: 2001:iv. |
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A descriptor for a non-lesion object finding or feature, used to indicate whether the object was detected as being internal or external to the patient's body. |
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A concept modifier for an Osseous Anatomy, or bone related, finding. |
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A text label used for tracking a finding or feature, potentially across multiple reporting objects, over time. This label shall be unique within the domain in which it is used. Corresponds to Tracking ID (0062,0020). |
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A unique identifier used for tracking a finding or feature, potentially across multiple reporting objects, over time. Corresponds to Tracking UID (0062,0021). |
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At least a 30% decrease in the sum of the Longest Diameter of target lesions, taking as reference the baseline sum Longest Diameter. |
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At least a 20% increase in the sum of the Longest Diameter of target lesions, taking as reference the smallest sum Longest Diameter recorded since the treatment started, or the appearance of one or more new lesions. |
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Neither sufficient shrinkage to qualify for Partial Response nor sufficient increase to qualify for Progressive Disease, taking as reference the smallest sum Longest Diameter since the treatment started. |
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Disappearance of all non-target lesions and normalization of tumor marker level. |
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Persistence of one or more non-target lesions and/or maintenance of tumor marker level above the normal limits. |
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Appearance of one or more new lesions and/or unequivocal progression of existing non-target lesions. |
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The current response evaluation for treatment of solid tumors, according to a method such as RECIST. |
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Best response recorded from the start of the treatment until disease progression/recurrence, taking as reference for Progressive Disease the smallest measurements recorded since the treatment started, according to a method such as RECIST. |
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A text identifier of an anatomic feature when a multiplicity of features of that type may be present, such as "Rib 1", "Rib 2" or thoracic vertebrae "T1" or "T2". |
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A measured or calculated evaluation of response. E.g., according to a method such as RECIST, the value would be the calculated sum of the lengths of the longest axes of a set of target lesions. |
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Of or relating to a bronchial (lung) specific channel for the conveyance of a body fluid. |
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The smallest unit of lung surrounded by connective tissue septa; the unit of lung subtended by any bronchiole that gives off three to five terminal bronchioles [Fraser and Pare]. |
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A method of calculating an overall calcium score, reflecting the calcification of coronary arteries, based on the maximum X-Ray attenuation coefficient and the area of calcium deposits. |
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A method of calculating an overall calcium score, reflecting the calcification of coronary arteries, based on the volume of each calcification, typically expressed in mm3. |
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A method of calculating an overall calcium score, reflecting the calcification of coronary arteries, based on the total mass of calcification, typically expressed in mg. |
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A measure often arrived at through calculation of findings from CT examination, which is a common predictor of significant stenosis of the coronary arteries. |
Retired. Replaced by (450360000, SCT, "Coronary artery calcium score") |
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The combination of a focus of pneumonia due to a primary infection with granulomas in the draining hilar or mediastinal lymph nodes [Fraser and Pare]. |
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General or local decrease in the apparent width of visible pulmonary vessels, suggesting less than normal blood flow (reduced blood flow) [Fraser and Pare]. |
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Linear opacity of very fine width, i.e., a nearly one dimensional opacity. |
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Area of abnormal very low X-Ray attenuation, typically lower than aerated lung when occurring in or projecting over lung, or lower than soft tissue when occurring in or projecting over soft tissue. |
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A calcific opacity within the lung that may be organized, but does not display the trabecular organization of true bone [Fraser and Pare]. |
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Relatively homogeneous, extended, pattern of abnormal opacity in the lung, typically low in contrast. |
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A collection of innumerable small, linear, and nodular opacities that together produce a composite appearance resembling a net with small superimposed nodules. The reticular and nodular elements are dimensionally of similar magnitude [Fraser and Pare]. |
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Irregular septal thickening that suggests the appearance of a row of beads; usually a sign of lymphangitic carcinomatosis, but may also occur rarely in sarcoidosis [Fraser and Pare]. |
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A collection of innumerable, small discrete opacities ranging in diameter from 2-10 mm, generally uniform in size and widespread in distribution, and without marginal spiculation [Fraser and Pare]. |
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An irregular band of peripheral pulmonary opacity adjacent to visceral pleura that simulates the appearance of a pleural plaque and is formed by coalescence of small nodules [Fraser and Pare] . |
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A ring of opacities (usually representing a dilated, thick-walled bronchus) in association with a smaller, round, soft tissue opacity (the adjacent pulmonary artery) suggesting a "signet ring" [Fraser and Pare]. |
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Equivalent of air bronchogram, but in airways assumed to be bronchioles because of peripheral location and diameter [Fraser and Pare]. |
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Radiographic shadow of an air-containing bronchus; presumed to represent an air-containing segment of the bronchial tree (identity often inferred) [Fraser and Pare]. |
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Air in a crescentic shape in a nodule or mass, in which the air separates the outer wall of the lesion from an inner sequestrum, which most commonly is a fungus ball of Aspergillusspecies [Fraser and Pare]. |
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Ground-glass opacity surrounding the circumference of a nodule or mass. May be a sign of invasive aspergillosis or hemorrhage of various causes [Fraser and Pare]. |
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Flag denoting that this lesion was identified, at baseline, as a target lesion intended for tracking over time [RECIST]. |
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Flag denoting that this lesion was not identified, at baseline, as a target lesion, and was not intended for tracking over time [RECIST]. |
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Flag denoting that this finding was identified, at baseline, as a category other than a lesion, and was not intended for tracking over time [RECIST]. |
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Local or general reduction in the caliber of visible pulmonary vessels, presumed to result from decreased flow occasioned by contraction of muscular pulmonary arteries [Fraser and Pare]. |
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Local or general increase in the width of visible pulmonary vessels resulting from increased pulmonary blood flow [Fraser and Pare]. |
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A manifestation of lung disease in which bronchi, pulmonary vessels, a fissure or fissures, or septa of secondary pulmonary lobules are abnormally displaced [Fraser and Pare]. |
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A patchwork of regions of varied attenuation, interpreted as secondary to regional differences in perfusion [Fraser and Pare]. |
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Increased blood flow to the lungs or a portion thereof, manifested by a general or local increase in the width of visible pulmonary vessels [Fraser and Pare]. |
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The common boundary between the shadows of two juxtaposed structures or tissues of different texture or opacity (edge, border) [Fraser and Pare]. |
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A longitudinal opacity no greater than 2 mm in width [Fraser and Pare]. |
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The shadow of an absorber that attenuates the primary X-Ray beam less effectively than do surrounding absorbers. In a radiograph, any circumscribed area that appears more nearly black (of greater photometric density) than its surround [Fraser and Pare]. |
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A midlung region, characterized by the absence of large blood vessels and by a paucity of small blood vessels, that corresponds to the minor fissure and adjacent peripheral lung [Fraser and Pare]. |
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The angle formed by the right and left main bronchi at the tracheal bifurcation [Fraser and Pare]. |
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The pulmonary artery and its immediate branches in a secondary lobule; HRCT depicts these vessels in certain cases; a.k.a. core structures or lobular core structures [Fraser and Pare]. |
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A vertically oriented linear or curvilinear opacity approximately 1-2 mm wide, commonly projected on the tracheal air shadow [Fraser and Pare]. |
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A vertically oriented, linear or curvilinear opacity approximately 2 mm wide, commonly projected on the tracheal air shadow, and usually slightly concave to the right [Fraser and Pare]. |
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A space in the right side of the mediastinum into which the medial edge of the right lower lobe extends [Fraser and Pare]. |
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A vertically oriented interface usually seen in a frontal chest radiograph to the left of the thoracic vertebral column [Fraser and Pare]. |
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A vertically oriented linear opacity ranging in width from 2-5 mm, extending from the thoracic inlet to the bifurcation of the trachea, and visible only on lateral radiographs of the chest [Fraser and Pare]. |
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A vertically oriented linear opacity approximately 2-3 mm wide extending from the thoracic inlet to the right tracheobronchial angle [Fraser and Pare]. |
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A longitudinal composite opacity measuring 2-5 mm in width; acceptable when limited to anatomic structures within the mediastinum [Fraser and Pare]. |
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A gap or passage through an anatomical part or organ; especially: a gap through which another part or organ passes. |
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A small rounded elevation or eminence on the first rib for the attachment of the scalenus anterior. |
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A groove that serves for the transmission of the vertebral artery. |
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The concave depression of the anterior surface of the scapula. |
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A sloping ridge dividing the dorsal surface of the scapula into the supraspinatous fossa (above), and the infraspinatous fossa (below). |
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The portion of the dorsal surface of the scapula above the scapular spine. |
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The portion of the dorsal surface of the scapula below the scapular spine. |
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The portion of the aortic arch that defines the transition between its ascending and descending limbs. |
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Section of Azygos vein near the fourth thoracic vertebra, where it arches forward over the root of the right lung, and ends in the superior vena cava, just before that vessel pierces the pericardium. |
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A local collection of gas and liquid that, when traversed by a horizontal X-Ray beam, creates a shadow characterized by a sharp horizontal interface between gas density above and liquid density below [Fraser and Pare]. |
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A circumferential pattern of fine linear spicules, approximately 5 mm long, extending outward from the margin of a solitary pulmonary nodule through a zone of relative lucency [Fraser and Pare]. |
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A number of closely approximated ring shadows representing air spaces 5-10 mm in diameter with walls 2-3 mm thick that resemble a true honeycomb; implies "end-stage" lung [Fraser and Pare]. |
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A straight, curved, or irregular linear opacity that is visible in multiple projections; usually situated in the lower half of the lung; vary markedly in length and width [Fraser and Pare]. |
|||
Fine linear opacities present in a lobule when the intralobular interstitium is thickened. When numerous, they may appear as a fine reticular pattern [Fraser and Pare]. |
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Essentially straight linear opacity 2-6 cm in length and 1-3 mm in width, usually in an upper lung zone [Fraser and Pare]. |
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A straight linear opacity 1.5-2 cm in length and 1-2 mm in width, usually at the lung base [Fraser and Pare]. |
|||
A group of branching, linear opacities producing the appearing of a fine net, at the lung base [Fraser and Pare]. |
|||
Elongated opacity, usually several millimeters wide and up to about 5 cm long, often extending to the pleura, which may be thickened and retracted at the site of contact [Fraser and Pare]. |
|||
A collection of innumerable small linear opacities that together produce an appearance resembling a net [Fraser and Pare]. |
|||
Usually used in the plural, a generic term for linear opacities of varied distribution produced when the interstitium between pulmonary lobules is thickened [Fraser and Pare]. |
|||
A thin curvilinear opacity, a few millimeters or less in thickness, usually less than 1 cm from the pleural surface and paralleling the pleura [Fraser and Pare]. |
|||
Parallel or slightly convergent linear opacities that suggest the planar projection of tubular structures and that correspond in location and orientation to elements of the bronchial tree [Fraser and Pare]. |
|||
Paired, parallel, or slightly convergent linear opacities presumed to represent the walls of a tubular structure seen en face; used if the anatomic nature of a shadow is obscure [Fraser and Pare]. |
|||
The opacity of a radiographic shadow to visible light; film blackening; the term should never be used to mean an "opacity" or "radiopacity" [Fraser and Pare]. |
|||
Subpleural increased attenuation in dependent lung. The increased attenuation disappears when the region of lung is nondependent; a.k.a. dependent increased attenuation [Fraser and Pare]. |
|||
Hazy increased attenuation of lung, but with preservation of bronchial and vascular margins; caused by partial filling of air spaces, interstitial thickening, partial collapse of alveoli, normal expiration, or increased capillary blood volume [Fraser and Pare]. |
|||
Discrete, small, round, focal opacity of at least soft tissue attenuation and with a diameter no greater than 7 mm [Fraser and Pare]. |
|||
A shadow produced by a local collection of fluid in one of the interlobar fissures, usually elliptic in one radiographic projection and rounded in the other, resembling a tumor [Fraser and Pare]. |
|||
Any perceptible discontinuity in film blackening attributed to the attenuation of the X-Ray beam by a specific anatomic absorber or lesion on or within the body of the patient; to be employed only when more specific identification is not possible [Fraser and Pare]. |
|||
Term used to define a reticular pattern specific to pneumoconioses [Fraser and Pare]. |
|||
Term used to define a nodular pattern specific to pneumoconioses [Fraser and Pare]. |
|||
Nodular dilation of centrilobular branching structures that resembles a budding tree and represents exudative bronchiolar dilation [Fraser and Pare]. |
|||
Any extended, finely granular pattern of pulmonary opacity within which normal anatomic details are partly obscured [Fraser and Pare]. |
|||
A collection of tiny discrete opacities in the lungs, each measuring 2 mm or less in diameter, generally uniform in size and widespread in distribution [Fraser and Pare]. |
|||
Generalized pattern of relatively well defined areas in the lung having different X-Ray attenuations due to a longstanding underlying |
|||
A qualitative descriptor of a size that is dramatically less than typical. |
|||
A qualitative descriptor of a size that is considerably less than typical. |
|||
A qualitative descriptor of a size that is so small as to be abnormal versus expected size. |
|||
A border shape that is made up of, provided with, or divided into lobules (small lobes, curved or rounded projections or divisions). |
|||
The border of a shadow (opacity) is sharply defined [Fraser and Pare]. |
|||
The border of a shadow (opacity) is distinctly defined [Fraser and Pare]. |
|||
The border of a shadow (opacity) is well distinct from adjacent structures [Fraser and Pare]. |
|||
The border of a shadow (opacity) is sharply distinct from adjacent structures [Fraser and Pare]. |
|||
The border of a shadow (opacity) is poorly distinct from adjacent structures [Fraser and Pare]. |
|||
A shadow (opacity) possessing a complete or nearly complete visible border [Fraser and Pare]. |
Retired. Replaced by (263706005, SCT, "Circumscribed") |
||
Inspired atmospheric gas. The word is sometimes used to describe gas within the body regardless of its composition or site [Fraser and Pare]. |
|||
Material having X-Ray attenuation properties similar to muscle. |
Retired. Replaced with (87784001, SCT, "Soft tissue"). |
||
Material having X-Ray attenuation properties similar to calcium, a silver-white bivalent metallic element occurring in plants and animals. |
|||
A pulmonary opacity 4-8 mm in diameter, presumed to represent anatomic acinus, or a collection of opacities in the lung, each measuring 4-8 mm in diameter, and together producing an extended, homogeneous shadow [Fraser and Pare]. |
|||
The gas-containing portion of the lung parenchyma, including the acini and excluding the interstitium [Fraser and Pare]. |
|||
Sharply defined, approximately circular opacities occurring singly or in clusters, usually in the upper lobes [Fraser and Pare]. |
|||
A shadow (opacity) that is ill-defined, lacking clear-cut margins [Fraser and Pare]. |
|||
A shadow resembling a line; any elongated opacity of approximately uniform width [Fraser and Pare]. |
|||
The number of small opacities per unit area or zone of lung. In the International Labor Organization (ILO) classification of radiographs of the pneumoconioses, the qualifiers 0 through 3 subdivide the profusion into 4 categories. The profusion categories may be further subdivided by employing a 12-point scale [Fraser and Pare]. |
|||
The effacement of an anatomic soft tissue border by either a normal anatomic structure or a pathologic state such as airlessness of adjacent lung or accumulation of fluid in the contiguous pleural space; useful in detecting and localizing an opacity along the axis of the X-Ray beam [Fraser and Pare]. |
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Replaced by (68599007, SCT, "Subpleural") |
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Spatial arrangement of opacities that bears vague resemblance to the shape of a bat in flight; bilaterally symmetric [Fraser and Pare]. |
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Spatial arrangement of opacities that bears vague resemblance to the shape of a butterfly in flight; bilaterally symmetric [Fraser and Pare]. |
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Referring to the region of the bronchioloarteriolar core of a secondary pulmonary lobule [Fraser and Pare]. |
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The joining together of a number of opacities into a single opacity [Fraser and Pare]. |
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Of or relating to a lobe (a curved or rounded projection or division). E.g., involving an entire lobe of the lung. |
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Extremely or excessively acute, as a qualitative measure of severity. |
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Discrete opacity centrally within a larger opacity, as a calcification descriptor. |
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Pertaining to sharply defined, linear, and/or nodular opacities containing calcification(s) [Fraser and Pare]. |
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Calcifications made up of loosely aggregated particles, resembling wool. |
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A change in the shape formed by the boundary or edges of a finding or feature. |
Retired. Replaced by (442755000, SCT, "Difference in border shape") |
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A change in the clarity of the boundary or edges of a finding or feature. |
Retired. Replaced by (442688001, SCT, "Difference in border definition") |
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A change in the extent of spreading of a finding or feature. |
Retired. Replaced by (442704007, SCT, "Difference in distribution") |
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A change in the part(s) of the anatomy affected or encompassed by a finding or feature. |
Retired. Replaced by (442711006, SCT, "Difference in site involvement") |
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A change in the matter or substance within a finding or feature. |
Retired. Replaced by (442691001, SCT, "Difference in substance") |
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A change in the surface or consistency of a finding or feature. |
Retired. Replaced by (442700003, SCT, "Difference in texture") |
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A location in image space, which may or may not correspond to an anatomical reference, which is often used for registering data. |
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Connected to an injection chamber placed under the skin in the upper part of the chest. When it is necessary to inject some drug, a specific needle is put in the chamber through the skin and a silicon membrane. The advantage of a portacath is that it may be left in place several months contrarily of "classical" catheters. |
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A tube inserted into the chest wall from outside the body, for drainage. Sometimes used for collapsed lung. Usually connected to a receptor placed lower than the insertion site. |
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A tube placed into the subclavian vein to deliver medication directly into the venous system. |
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A stent is a tube inserted into another tube. Kidney stent is a tube that is inserted into the kidney, ureter, and bladder, to help drain urine. Usually inserted through a scoping device presented through the urethra. |
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A stent is a tube inserted into another tube. Pancreatic stent is inserted through the common bile duct to the pancreatic duct, to drain bile. |
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A non-lesion object that appears to be a circular band, attached to the body via pierced nipple. |
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A non-lesion object that appears to be a flat round piece of metal. |
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The least quantity assignable, admissible, or possible; the least of a set of X-Ray attenuation coefficients. |
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The greatest quantity or value attainable or attained; the largest of a set of X-Ray attenuation coefficients. |
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The value that is computed by dividing the sum of a set of X-Ray attenuation coefficients by the number of values . |
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The value in an ordered set of X-Ray attenuation coefficients, below and above which there is an equal number of values. |
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For a set of X-Ray attenuation coefficients: 1) a measure of the dispersion of a frequency distribution that is the square root of the arithmetic mean of the squares of the deviation of each of the class frequencies from the arithmetic mean of the frequency distribution; 2) a parameter that indicates the way in which a probability function or a probability density function is centered around its mean and that is equal to the square root of the moment in which the deviation from the mean is squared. |
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American College of Radiology. ACR Standard for the Performance of Pediatric and Adult Thoracic Computed Tomography (CT). In: Standards. Reston, Va: 2001:103-107. |
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Performance of CT for Detection of Pulmonary Embolism in Adults |
American College of Radiology. ACR Standard for the Performance of Computed Tomography for the Detection of Pulmonary Embolism in Adults. In: Standards. Reston, Va: 2001:109-113. |
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American College of Radiology. ACR Standard for the Performance of High-Resolution Computed Tomography (HRCT) of the Lungs in Adults. In: Standards. Reston, Va: 2001:115-118. |
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The method of calculation of a measurement or other type of numeric value is not specified. |
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The calculation method was performed in two-dimensional space. |
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The calculation method was performed in three-dimensional space. |
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The relative density of parenchymal tissue as a proportion of breast volume. |
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A measured or calculated percentage of vascular calcification. |
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The average nearest neighbor distance of all individual microcalcifications in a cluster. |
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The standard deviation of nearest neighbor distance of all individual microcalcifications in a cluster. |
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A structured report containing the results of computer-aided detection or diagnosis applied to colon imaging and associated clinical information. |
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Overall interpretation of the colon using C-RADS categorization system. |
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Distance between contiguous images, measured from the center-to-center of each image. |
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Uniquely identifies groups of composite instances that have the same coordinate system that conveys spatial and/or temporal information. |
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Patient orientation with respect to downward direction (gravity). |
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The diameter of a polyp stalk measured perpendicular to the axis of the stalk. |
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The length of the path following the centerline of the colon from the anus to the area of interest. |
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An inadequate study or a study that is awaiting prior comparisons. The study may have inadequate preparation and cannot exclude lesions greater than or equal to ten millimeters owing to presence of fluid or feces. The study may have inadequate insufflation where one or more colonic segments collapsed on both views. Based on "CT Colonography Reporting and Data System: A Consensus Proposal", Radiology, July 2005; 236:3-9. |
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The study has a normal colon or benign lesion, with the recommendation to continue routine screening. The study has no visible abnormalities of the colon. The study has no polyps greater than six millimeters. The study may have lipoma, inverted diverticulum, or nonneoplastic findings, such as colonic diverticula. Based on "CT Colonography Reporting and Data System: A Consensus Proposal", Radiology, July 2005; 236:3-9. |
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The study has an intermediate polyp or indeterminate finding and surveillance or colonoscopy is recommended. There may be intermediate polyps between six and nine millimeters and there are less than three in number. The study may have an intermediate finding and cannot exclude a polyp that is greater than or equal to six millimeters in a technically adequate study. Based on "CT Colonography Reporting and Data System: A Consensus Proposal", Radiology, July 2005; 236:3-9. |
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The study has a polyp, possibly advanced adenoma, and a follow-up colonoscopy is recommended. The study has a polyp greater than or equal to ten millimeters or the study has three or more polyps that are each between six to nine millimeters. Based on "CT Colonography Reporting and Data System: A Consensus Proposal", Radiology, July 2005; 236:3-9. |
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The study has a colonic mass, likely malignant, and surgical consultation is recommended. The lesion compromises bowel lumen and demonstrates extracolonic invasion. Based on "CT Colonography Reporting and Data System: A Consensus Proposal", Radiology, July 2005; 236:3-9. |
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American College of Radiology Practice Guideline for the Performance of Computed Tomography (CT) Colonography in Adults. In: Practice Guidelines and Technical Standards.Reston, Va: American College of Radiology;2006:371-376. |
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American College of Radiology Technical Standard for Diagnostic Medical Physics Performance Monitoring of Computed Tomography (CT) Equipment. In: Practice Guidelines and Technical Standards.Reston, Va: American College of Radiology;2006:945-948. |
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View Orientation Modifier indicates that the view orientation of the imaging plane is rotated +45° along the cranial-caudal axis. |
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View Orientation Modifier indicates that the view orientation of the imaging plane is rotated -45° along the cranial-caudal axis. |
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Prosthetic component implanted into the acetabulum. Provides hold for the insert that is mounted inside the cup. ![]()
|
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Prosthetic pelvic joint component. Inserted into the cup, takes in the femoral head replacement. ![]()
|
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Prosthetic pelvic joint cup including insert. ![]()
|
|||
Component for Femoral Head Prosthesis where the conic intake for the stem neck can be exchanged. Combined with a Femoral Head Cone Taper Component. ![]()
|
|||
Exchangeable neck intake for composite femoral head prosthesis. |
|||
Prosthesis Implanted into the femoral bone to provide force transmission between joint replacement and bone. On the proximal end a conic neck holds the femoral head replacement. ![]()
|
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Distal half of a modular stem prosthesis system. Combined with a Stem Proximal Component. ![]()
|
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Proximal half of a modular stem prosthesis system. Combined with a Stem Distal Component. ![]()
|
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Stem prosthetic component with a modular insert for an exchangeable neck component. Combined with a Neck Component. ![]()
|
|||
Prosthetic Neck to be combined with a Stem Component. ![]()
|
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Prosthetic Stem and Femoral Head in one piece. ![]()
|
|||
A proximal attachment to the shaft used to compensate for bone deficiencies or bone loss. ![]()
|
|||
Artificial femur head surface needed for the partial replacement of the femoral head where only the surface is replaced. ![]()
|
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Attachment to the distal end of a cemented stem assuring that the stem is in a central position inside the drilled femoral canal before cementation. ![]()
|
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Planning of Hip Replacement according to the procedure of M. E. Müller [Eggli et. al.1998]. |
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A Report containing the results of an Implantation Planning Activity. |
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An implant template describing the properties (2D/3D geometry and other data) of one Implant Component. |
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ID of the Mating Feature in a Mating Feature Set in an Implant Component. |
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A collection of Component Connections of Implant Components. |
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Fiducials that are selected by the user and may or may not belong to anatomical landmarks. |
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Fiducials that represent geometric characteristics, such as center of rotation, and are derived from other fiducials. |
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All parameters and data that were used for the planning activity. |
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A list of all Implant Components selected for an implantation. |
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Reference to objects containing patient data that is used for planning. |
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A specification of the values from one or more Degrees of Freedom. |
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Reference to objects containing patient data that were not used for planning but are somehow related. |
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Implantation Reports that are somehow related. E.g., contemporaneous implantations that are independent. |
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One Implant Component that is connected to another Implant Component. |
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Procedure step protocol for photographic imaging of surgical procedures, including photography of specimens collected. |
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Procedure step protocol for imaging gross specimens, typically with a photographic camera (modality XC), and planning further dissection. |
Retired. Replaced with (168456004, SCT, "Gross pathology request") |
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Procedure step protocol for imaging slide specimens using a whole slide scanner. |
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Procedure step protocol for imaging slide specimens using a whole slide scanner with a 20X nominal objective lens, in full color, with a single imaging focal plane across the image. |
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Procedure step protocol for imaging slide specimens using a whole slide scanner with a 40X nominal objective lens, in full color, with a single imaging focal plane across the image. |
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Nominal distance above a reference plane (typically a slide glass substrate top surface) of the focal plane. |
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Microscope magnification based on nominal objective lens power. |
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Technique for identifying tissue to be imaged versus area of slide not to be imaged. |
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Nominal 5 power objective lens, resulting in a digital image at approximately 2 um/pixel spacing. |
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Nominal 10 power objective lens, resulting in a digital image at approximately 1 um/pixel spacing. |
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Nominal 20 power microscope objective lens, resulting in a digital image at approximately 0.5 um/pixel spacing. |
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Nominal 40 power microscope objective lens, with a combined condenser and objective lens numerical aperture of approximately 1.3, resulting in a digital image at approximately 0.25 um/pixel spacing. |
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Equipment-specific nominal or default method for identifying tiles without tissue imaged for suppression from inclusion in image object. |
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Equipment-specific high threshold method for identifying tiles without tissue imaged for suppression from inclusion in image object. |
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Tiles without tissue imaged are not suppressed from inclusion in image object. |
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A selection that represents the "best" chosen from a larger set of items. E.g., the best images within a Study or Series. The criteria against which "best" is measured is not defined. Contrast this with the more specific term "Best illustration of finding". |
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A study is a collection of one or more series of medical images, presentation states, and/or SR documents that are logically related for the purpose of diagnosing a patient. A study may include composite instances that are created by a single modality, multiple modalities or by multiple devices of the same modality. [From Section A.1.2.2 “Study IE” in PS3.3 ] |
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A distinct logical set used to group composite instances. All instances within a Series are of the same modality, in the same Frame of Reference (if any), and created by the same equipment. [See Section A.1.2.3 “Series IE” in PS3.3 ] |
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An arbitrarily defined unit of service that has actually been performed (not just scheduled). [From Section 7.3.1.9 “Modality Performed Procedure Step” in PS3.3 ] |
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An image or set of images illustrating a specific stage (phase in a stress echo study protocol) and view (combination of the transducer position and orientation at the time of image acquisition). |
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Selection of information objects for attachment to the clinical report of the Current Requested Procedure. |
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List of objects that are related to litigation and should be specially handled. E.g., may apply if a complaint has been received regarding a patient, or a specific set of images has been the subject of a subpoena, and needs to be sequestered or excluded from automatic purging according to retention policy. |
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This Key Object Selection Document references Presentation State instances that are related, which may or may not share a value of Presentation Display Collection UID (0070,1101) or Presentation Sequence Collection UID (0070,1102). |
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A list of objects that have been exported out of one organizational domain into another domain. Typically, the first domain has no direct control over what the second domain will do with the objects. |
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A signed list of objects that have been exported out of one organizational domain into another domain, referenced securely with either Digital Signatures or MACs. Typically, the first domain has no direct control over what the second domain will do with the objects. |
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The list of objects that constitute a study at the time that the list was created. |
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The signed list of objects that constitute a study at the time that the list was created, referenced securely with either Digital Signatures or MACs. |
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The list of objects that were generated in a single procedure step. |
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The signed list of objects that were generated in a single procedure step, referenced securely with either Digital Signatures or MACs. |
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A list of frames or single-frame or entire multi-frame instances that together constitute a set for some purpose, such as might be displayed together in the same viewport, as distinct from another set that might be displayed in a separate viewport. |
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List of objects whose use is potentially harmful to the patient. E.g., an improperly labeled image could lead to dangerous surgical decisions. |
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List of objects that were acquired using an incorrect modality worklist entry, and that should not be used, since they may be incorrectly identified. |
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List of objects that have expired according to a defined data retention policy. |
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Values are derived by calculation of the apparent diffusion coefficient. This concept may be used for the diffusion coefficient of various different models, e.g., mono-exponential (ADCm), kurtosis (ADCk), stretched-exponential (ADCs). The "apparent" appellation is because the diffusion images from which the ADC is computed may also be affected by T2 contrast (T2 "shine-through"), so this concept is distinguished from a "pure" diffusion coefficient that is not so affected. |
Graessner J. Frequently Asked Questions: Diffusion-Weighted Imaging (DWI). MAGNETOM Flash. Siemens. 2011 Jan. http://clinical-mri.com/wp-content/uploads/software_hardware_updates/Graessner.pdf Toivonen J, Merisaari H, Pesola M, Taimen P, Boström PJ, Pahikkala T, et al. Mathematical models for diffusion-weighted imaging of prostate cancer using b values up to 2000 s/mm2: Correlation with Gleason score and repeatability of region of interest analysis. Magnetic Resonance in Medicine. 2015;74(4):1116-24. http://dx.doi.org/10.1002/mrm.25482 |
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Values are derived by the pixel by pixel addition of two images. |
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Values are derived by calculation of the diffusion weighting. |
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Values are derived by calculation of the diffusion anisotropy. |
|||
Values are derived by calculation of the diffusion attenuation. |
|||
Values are derived by the pixel by pixel division of two images. |
|||
Values are derived by the pixel by pixel masking of one image by another. |
|||
Values are derived by calculating the pixel by pixel maximum of two or more images. |
|||
Values are derived by calculating the pixel by pixel mean of two or more images. |
|||
Values are derived by calculating from spectroscopy data pixel values localized in two dimensional space based on the concentration of specific metabolites (i.e, at specific frequencies). |
|||
Values are derived by calculating the pixel by pixel minimum of two or more images. |
|||
The time required for blood to pass through a region of tissue. |
|||
Values are derived by the pixel by pixel multiplication of two images. |
|||
The area described by the baseline and the signal loss due to passage of contrast bolus in tissue in a perfusion experiment. Abbreviated NEI or N1. |
|||
The absolute flow rate of blood perfusing a region of the brain as volume per mass per unit of time. The mass divisor may be approximated by a measurement of volume assuming a tissue density of 1. |
|||
The absolute volume of blood perfusing a region of brain as volume per mass. The mass divisor may be approximated by a measurement of volume assuming a tissue density of 1. |
|||
Values are derived by calculating the standard deviation of two or more images. |
|||
Values are derived by the pixel by pixel subtraction of two images. |
|||
The time constant for the decay of longitiudinal magnetization caused by spin-lattice relaxation. The inverse of the longitudinal relaxation rate constant, i.e., T1 = 1/R1. |
|||
The time constant for the decay of transverse magnetization caused by a combination of spin-spin relaxation and magnetic field inhomogeneity. The inverse of the transverse relaxation rate constant, i.e., T2* = 1/R2*. |
|||
The time constant for the decay of transverse magnetization caused by spin-spin relaxation. The inverse of the transverse relaxation rate constant, i.e., T2 = 1/R2. |
|||
Values are derived by calculating values based on temperature encoding. |
|||
Values are derived by calculating the value of the Student's T-Test statistic from multiple image samples. |
|||
The time from the start of the contrast agent injection to the maximum enhancement value. |
|||
Values are derived by calculating values based on velocity encoded. E.g., phase contrast. |
|||
Values are derived by calculating the value of the Z-Score statistic from multiple image samples. |
|||
Values are derived by reformatting in a flat plane other than that originally acquired. |
|||
Values are derived by reformatting in a curve plane other than that originally acquired. |
|||
Values are derived by segmentation (classification into tissue types) of acquired data. |
|||
Values are derived by selectively editing acquired data (removing values from the volume), such as in order to remove obscuring structures or noise. |
|||
Values are derived by maximum intensity projection of acquired data. |
|||
Values are derived by minimum intensity projection of acquired data. |
|||
For single-proton MR spectroscopy, the resonance peak corresponding to glutamate and glutamine. |
|||
For single-proton MR spectroscopy, the ratio between the Choline and Creatine resonance peaks. |
|||
For single-proton MR spectroscopy, the ratio between the N-acetylaspartate and Creatine resonance peaks. |
|||
For single-proton MR spectroscopy, the ratio between the N-acetylaspartate and Choline resonance peaks. |
|||
The time delay to the maximum of the residue function after deconvolution. Shih LC, Saver JL, Alger JR, Starkman S, Leary MC, Vinuela F, et al. Perfusion-Weighted Magnetic Resonance Imaging Thresholds Identifying Core, Irreversibly Infarcted Tissue. Stroke. 2003 Jun 1;34(6):1425-30. doi:10.1161/01.STR.0000072998.70087.E9. http://stroke.ahajournals.org/content/34/6/1425.abstract Østergaard L, Weisskoff RM, Chesler DA, Gyldensted C, Rosen BR. High resolution measurement of cerebral blood flow using intravascular tracer bolus passages. Part I: Mathematical approach and statistical analysis. Magnetic Resonance in Medicine. 1996;36(5):715-25. doi:10.1002/mrm.1910360510. http://onlinelibrary.wiley.com/doi/10.1002/mrm.1910360510/abstract |
|||
Values are derived by stitching two or more images together. |
|||
Spatially-related frames in this image are representative frames from the referenced 3D volume data. |
|||
Temporally-related frames in this image are representative frames from the referenced 3D volume data. |
|||
Conversion of a polar coordinate image to rectangular (Cartesian) coordinate image. |
|||
For single-proton MR spectroscopy, the resonance peak corresponding to creatine and choline. |
|||
For single-proton MR spectroscopy, the resonance peak corresponding to lipid and lactate. |
|||
For single-proton MR spectroscopy, the ratio between the Choline and Creatine resonance peak and the Citrate resonance peak. |
|||
Image pixels created through proportional weighting of multiple acquisitions at distinct X-Ray energies. |
|||
Magnetization Transfer Ratio (MTR) is the ratio of magnetization transfer, Mo - Ms/Mo, where Ms represents the magnitude of signal of tissues with the saturation pulse used to saturate macromolecular protons on, and Mo is the magnitude of signal without saturation. See Dousset V, Grossman RI, Ramer KN, Schnall MD, Young LH, Gonzalez-Scarano F, et al. Experimental allergic encephalomyelitis and multiple sclerosis: lesion characterization with magnetization transfer imaging. Radiology. 1992 Feb 1;182(2):483-91. http://dx.doi.org/10.1148/radiology.182.2.1732968 |
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De-identification using a profile defined in PS3.15 that requires removing all information related to the identity and demographic characteristics of the patient, any responsible parties or family members, any personnel involved in the procedure, the organizations involved in ordering or performing the procedure, additional information that could be used to match instances if given access to the originals, such as UIDs, dates and times, and Private Attributes, when that information is present in the non-Pixel Data Attributes, including graphics or overlays. |
|||
Additional de-identification according to an option defined in PS3.15 that requires any information burned in to the Pixel Data corresponding to the Attribute information specified to be removed by the Profile and any other Options specified also be removed. |
|||
Additional de-identification according to an option defined in PS3.15 that requires that sufficient removal or distortion of the Pixel Data shall be applied to prevent recognition of an individual from the instances themselves or a reconstruction of a set of instances. |
|||
Additional de-identification according to an option defined in PS3.15 that requires that any information encoded in graphics, text annotations or overlays corresponding to the Attribute information specified to be removed by the Profile and any other Options specified also be removed. |
|||
Additional de-identification according to an option defined in PS3.15 that requires that any information encoded in SR Content Items or Acquisition Context Sequence Items corresponding to the Attribute information specified to be removed by the Profile and any other Options specified also be removed. |
|||
Additional de-identification according to an option defined in PS3.15 that requires that any information that is embedded in text or string Attributes corresponding to the Attribute information specified to be removed by the Profile and any other Options specified also be removed. |
|||
Retention of information that would otherwise be removed during de-identification according to an option defined in PS3.15 that requires that any dates and times be retained,. |
|||
Retain Longitudinal Temporal Information Modified Dates Option |
Retention of information that would otherwise be removed during de-identification according to an option defined in PS3.15 that requires that any dates and times be modified in a manner that preserves temporal relationships. E.g., Study Date and Time. |
||
Retention of information that would otherwise be removed during de-identification according to an option defined in PS3.15 that requires that any physical characteristics of the patient, which are descriptive rather than identifying information per se, be retained. E.g., Patient's Age, Sex, Size (height) and Weight. |
|||
Retention of information that would otherwise be removed during de-identification according to an option defined in PS3.15 that requires that any information that identifies a device be retained. E.g., Device Serial Number. |
|||
Retention of information that would otherwise be removed during de-identification according to an option defined in PS3.15 that requires that UIDs be retained. E.g., SOP Instance UID. |
|||
Retention of information that would otherwise be removed during de-identification according to an option defined in PS3.15 that requires that Private Attributes that are known not to contain identity information be retained. E.g., private SUV scale factor. |
|||
Retention of information that would otherwise be removed during de-identification according to an option defined in PS3.15 that requires that any information that identifies an institution be retained. E.g., Institution Name. |
|||
Images used as the source for an image processing operation that extracts data for a single subject from an image containing data for multiple subjects (e.g., a group of animals imaged simultaneously). |
|||
An image processing operation that extracts data for a single subject from an image containing data for multiple subjects (e.g., a group of animals imaged simultaneously). |
|||
A single subject that has been selected from amongst multiple subjects (e.g., a group of animals imaged simultaneously). |
|||
Sum of the diffusion tensor eigenvalues. I.e.: Tr = λ1+ λ2+ λ3, where λ1 ≥ λ2 ≥ λ3. Reference: Winston GP. The physical and biological basis of quantitative parameters derived from diffusion MRI. Quantitative Imaging in Medicine and Surgery. 2012;2(4) :254-265. doi:10.3978/j.issn.2223-4292.2012.12.05. (http://www.ncbi.nlm.nih.gov/pmc/articles/PMC3533595/) |
|||
Average of the diffusion tensor eigenvalues in all directions. Reference: Winston GP. The physical and biological basis of quantitative parameters derived from diffusion MRI. Quantitative Imaging in Medicine and Surgery. 2012;2(4) :254-265. doi:10.3978/j.issn.2223-4292.2012.12.05. (http://www.ncbi.nlm.nih.gov/pmc/articles/PMC3533595/) |
|||
Average of the two non-principal (i.e., perpendicular) diffusion tensor eigenvalues(also known as transverse diffusivity, perpendicular diffusivity). Reference: Winston GP. The physical and biological basis of quantitative parameters derived from diffusion MRI. Quantitative Imaging in Medicine and Surgery. 2012;2(4) :254-265. doi:10.3978/j.issn.2223-4292.2012.12.05. (http://www.ncbi.nlm.nih.gov/pmc/articles/PMC3533595/) |
|||
Diffusion tensor eigenvalue of the principal axis (also known as longitudinal diffusivity, parallel diffusivity). Reference: Winston GP. The physical and biological basis of quantitative parameters derived from diffusion MRI. Quantitative Imaging in Medicine and Surgery. 2012;2(4) :254-265. doi:10.3978/j.issn.2223-4292.2012.12.05. (http://www.ncbi.nlm.nih.gov/pmc/articles/PMC3533595/) |
|||
MK = diffusional kurtosis averaged over all gradient directions Reference: Tabesh A, Jensen JH, Ardekani BA, Helpern JA. Estimation of Tensors and Tensor-Derived Measures in Diffusional Kurtosis Imaging. Magnetic Resonance in Medicine. 2011;65(3) :823-836. doi:10.1002/mrm.22655. (http://www.ncbi.nlm.nih.gov/pmc/articles/PMC3042509/) Reference: Liu C, Mang SC, Moseley ME. In VivoGeneralized Diffusion Tensor Imaging (GDTI) Using Higher-Order Tensors (HOT). Magnetic resonance in medicine : official journal of the Society of Magnetic Resonance in Medicine / Society of Magnetic Resonance in Medicine. 2010;63(1) :243-252. doi:10.1002/mrm.22192. (http://www.ncbi.nlm.nih.gov/pmc/articles/PMC2824337/) |
|||
AKC = diffusional kurtosis in a given direction Reference: Liu C, Mang SC, Moseley ME. In VivoGeneralized Diffusion Tensor Imaging (GDTI) Using Higher-Order Tensors (HOT). Magnetic resonance in medicine : official journal of the Society of Magnetic Resonance in Medicine / Society of Magnetic Resonance in Medicine. 2010;63(1) :243-252. doi:10.1002/mrm.22192. (http://www.ncbi.nlm.nih.gov/pmc/articles/PMC2824337/) |
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KR = diffusional kurtosis perpendicular to the direction of the highest diffusion (also known as transverse kurtosis, perpendicular kurtosis) Reference: Tabesh A, Jensen JH, Ardekani BA, Helpern JA. Estimation of Tensors and Tensor-Derived Measures in Diffusional Kurtosis Imaging. Magnetic Resonance in Medicine. 2011;65(3) :823-836. doi:10.1002/mrm.22655. (http://www.ncbi.nlm.nih.gov/pmc/articles/PMC3042509/) |
|||
KA = diffusional kurtosis in the direction of the highest diffusion (also known as longitudinal kurtosis, parallel kurtosis) Reference: Tabesh A, Jensen JH, Ardekani BA, Helpern JA. Estimation of Tensors and Tensor-Derived Measures in Diffusional Kurtosis Imaging. Magnetic Resonance in Medicine. 2011;65(3) :823-836. doi:10.1002/mrm.22655. (http://www.ncbi.nlm.nih.gov/pmc/articles/PMC3042509/) |
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FKA = fractional kurtosis of diffusion in tissues Reference: Liu C, Mang SC, Moseley ME. In VivoGeneralized Diffusion Tensor Imaging (GDTI) Using Higher-Order Tensors (HOT). Magnetic resonance in medicine : official journal of the Society of Magnetic Resonance in Medicine / Society of Magnetic Resonance in Medicine. 2010;63(1) :243-252. doi:10.1002/mrm.22192. (http://www.ncbi.nlm.nih.gov/pmc/articles/PMC2824337/) |
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Tracking based on local directionality Reference: Descoteaux M, Deriche R, Knösche TR, Anwander A. Deterministic and probabilistic tractography based on complex fibre orientation distributions. IEEE Trans Med Imaging.2009; 28(2) :269-86 (http://www.ncbi.nlm.nih.gov/pubmed/19188114) |
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Tracking using local fiber orientation likelihood derive global connectivity likelihood Reference: Descoteaux M, Deriche R, Knösche TR, Anwander A. Deterministic and probabilistic tractography based on complex fibre orientation distributions. IEEE Trans Med Imaging.2009; 28(2) :269-86 (http://www.ncbi.nlm.nih.gov/pubmed/19188114) |
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Tracking allfibers simultaneously, searching for a global optimum. Reference: Reisert M, Mader I, Anastasopoulos C, Weigel M, Schnell S, Kiselev V. Global fiber reconstruction becomes practical. NeuroImage. 2011 Jan 15;54(2) :955-62. (http://www.ncbi.nlm.nih.gov/pubmed/20854913) |
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Fiber Assessment by Continuous Tracking Reference: Mori S, Crain BJ, Chacko VP, van Zijl PC. Three-dimensional tracking of axonal projections in the brain by magnetic resonance imaging. Ann Neurol . 1999 Feb;45(2) :265-9 (http://www.ncbi.nlm.nih.gov/pubmed/9989633) Reference: Descoteaux M, Deriche R, Knösche TR, Anwander A. Deterministic and probabilistic tractography based on complex fibre orientation distributions. IEEE Trans Med Imaging.2009; 28(2) :269-86 (http://www.ncbi.nlm.nih.gov/pubmed/19188114) |
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Streamline tracking techniques (STT) Reference: Basser PJ, Pajevic S, Pierpaoli C, Duda J, Aldroubi A. In vivo fiber tractography using DT-MRI data. Magn Reson Med. 2000 Oct;44(4) :625-32 (http://www.ncbi.nlm.nih.gov/pubmed/11025519) |
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Reference: Lazar M, Weinstein DM, Tsuruda JS, Hasan KM, Arfanakis K, Meyerand ME, Badie B, Rowley HA, Haughton V, Field A, Alexander AL. White matter tractography using diffusion tensor deflection. Hum Brain Mapp.2003 Apr;18(4) :306-21. (http://www.ncbi.nlm.nih.gov/pubmed/12632468) |
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Non-parametric estimation of fiber tracking dispersion Reference: Lazar M, Alexander AL. Bootstrap white matter tractography (BOOT-TRAC). Neuroimage. 2005 Jan 15;24(2) :524-32. Epub 2004 Nov 24. (http://www.ncbi.nlm.nih.gov/pubmed/15627594) Reference: Jones DK, Pierpaoli C. Confidence mapping in diffusion tensor magnetic resonance imaging tractography using a bootstrap approach. Magn Reson Med.2005 May;53(5) :1143-9. (http://www.ncbi.nlm.nih.gov/pubmed/15844149) |
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Reference: Basser PJ, Pajevic S, Pierpaoli C, Duda J, Aldroubi A. In vivo fiber tractography using DT-MRI data. Magn Reson Med. 2000 Oct;44(4) :625-32 (http://www.ncbi.nlm.nih.gov/pubmed/11025519) Reference: Descoteaux M, Deriche R, Knösche TR, Anwander A. Deterministic and probabilistic tractography based on complex fibre orientation distributions. IEEE Trans Med Imaging.2009; 28(2) :269-86 (http://www.ncbi.nlm.nih.gov/pubmed/19188114) |
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Integration method, 2nd or 4th order Reference: Basser PJ, Pajevic S, Pierpaoli C, Duda J, Aldroubi A. In vivo fiber tractography using DT-MRI data. Magn Reson Med. 2000 Oct;44(4) :625-32 (http://www.ncbi.nlm.nih.gov/pubmed/11025519) |
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High Angular Resolution Diffusion Imaging Reference: Tuch DS, Reese TG, Wiegell MR, Makris N, Belliveau JW, Wedeen VJ. High angular resolution diffusion imaging reveals intravoxel white matter fiber heterogeneity. Magn Reson Med.2002 Oct;48(4) :577-82. (http://www.ncbi.nlm.nih.gov/pubmed/12353272) Reference: Descoteaux M, Deriche R, Knösche TR, Anwander A. Deterministic and probabilistic tractography based on complex fibre orientation distributions. IEEE Trans Med Imaging.2009; 28(2) :269-86 (http://www.ncbi.nlm.nih.gov/pubmed/19188114) |
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Diffusion(al) Kurtosis Imaging Reference: Jensen JH, Helpern JA, Ramani A, Lu H, Kaczynski K. Diffusional kurtosis imaging: the quantification of non-gaussian water diffusion by means of magnetic resonance imaging. Magn Reson Med. 2005 Jun;53(6) :1432-40. (http://www.ncbi.nlm.nih.gov/pubmed/15906300) |
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Reference: Winston GP. The physical and biological basis of quantitative parameters derived from diffusion MRI. Quantitative Imaging in Medicine and Surgery. 2012;2(4) :254-265. doi:10.3978/j.issn.2223-4292.2012.12.05. (http://www.ncbi.nlm.nih.gov/pmc/articles/PMC3533595/) |
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Reference: Wedeen VJ, Wang RP, Schmahmann JD, Benner T, Tseng WY, Dai G, Pandya DN, Hagmann P, D'Arceuil H, de Crespigny AJ. Diffusion spectrum magnetic resonance imaging (DSI) tractography of crossing fibers. Neuroimage. 2008 Jul 15;41(4) :1267-77. doi:10.1016/j.neuroimage.2008.03.036. (http://www.ncbi.nlm.nih.gov/pubmed/18495497) Reference: Hagmann P, Jonasson L, Maeder P, Thiran JP, Wedeen VJ, Meuli R. Understanding diffusion MR imaging techniques: from scalar diffusion-weighted imaging to diffusion tensor imaging and beyond. Radiographics.2006 Oct;26 Suppl 1:S205-23. (http://www.ncbi.nlm.nih.gov/pubmed/17050517) |
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Line Scan Diffusion Imaging sequence Reference: Gudbjartsson H, Maier SE, Mulkern RV, Mórocz IA, Patz S, Jolesz FA. Line scan diffusion imaging. Magn Reson Med.1996 Oct;36(4) :509-19. (http://www.ncbi.nlm.nih.gov/pubmed/8892201) |
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An Echo Planar Imaging sequence in which the entire range of phase encoding steps is acquired in one repetition. Reference: Turner R, Le Bihan D, Chesnick AS. Echo-planar imaging of diffusion and perfusion. Magn Reson Med.1991 Jun;19(2) :247-53. (http://www.ncbi.nlm.nih.gov/pubmed/1881311) |
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An Echo Planar Imaging sequence in which separate parts of the range of phase encoding steps are acquired in multiple repetitions. Reference: Robson MD, Anderson AW, Gore JC. Diffusion-weighted multiple shot echo planar imaging of humans without navigation. Magn Reson Med.1997 Jul;38(1) :82-8. (http://www.ncbi.nlm.nih.gov/pubmed/9211383) |
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A imaging sequence that uses a subset of k-space data from an array of receiver coils, e.g., Sensitivity Encoding. Reference: Pruessmann KP, Weiger M, Scheidegger MB, Boesiger P. SENSE: sensitivity encoding for fast MRI. Magn Reson Med.1999 Nov;42(5) :952-62. (http://www.ncbi.nlm.nih.gov/pubmed/10542355) Reference: Deshmane A, Gulani V, Griswold MA, Seiberlich N. Parallel MR imaging. J Magn Reson Imaging. 2012 Jul;36(1) :55-72. (http://www.ncbi.nlm.nih.gov/pubmed/22696125) |
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Modeling anisotropic diffusion in a volume with a tensor following a Gaussian distribution (six degrees of freedom) Reference: Basser PJ, Mattiello J, LeBihan D. Estimation of the effective self-diffusion tensor from the NMR spin echo. J Magn Reson B.1994 Mar;103(3) :247-54. (http://www.ncbi.nlm.nih.gov/pubmed/8019776) Reference: Hagmann P1, Jonasson L, Maeder P, Thiran JP, Wedeen VJ, Meuli R. Understanding diffusion MR imaging techniques: from scalar diffusion-weighted imaging to diffusion tensor imaging and beyond. Radiographics.2006 Oct;26 Suppl 1:S205-23. (http://www.ncbi.nlm.nih.gov/pubmed/17050517) |
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Modeling anisotropic diffusion in a volume by fitting of multiple tensors Reference: Ozarslan E, Mareci TH. Generalized diffusion tensor imaging and analytical relationships between diffusion tensor imaging and high angular resolution diffusion imaging. Magn Reson Med.2003 Nov;50(5) :955-65. (http://www.ncbi.nlm.nih.gov/pubmed/14587006) Reference: Pasternak O, Assaf Y, Intrator N, Sochen N. Variational multiple-tensor fitting of fiber-ambiguous diffusion-weighted magnetic resonance imaging voxels. Magn Reson Imaging.2008 Oct;26(8) :1133-44. doi:10.1016/j.mri.2008.01.006. (http://www.ncbi.nlm.nih.gov/pubmed/18524529) |
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Reconstruction of anisotropic diffusion in a volume without imposing an underlying statistical model (data-driven approach) Reference: Wedeen VJ, Hagmann P, Tseng WY, Reese TG, Weisskoff RM. Mapping complex tissue architecture with diffusion spectrum magnetic resonance imaging. Magn Reson Med.2005 Dec;54(6) :1377-86. (http://www.ncbi.nlm.nih.gov/pubmed/16247738) Reference: Hagmann P, Jonasson L, Maeder P, Thiran JP, Wedeen VJ, Meuli R. Understanding diffusion MR imaging techniques: from scalar diffusion-weighted imaging to diffusion tensor imaging and beyond. Radiographics.2006 Oct;26 Suppl 1:S205-23. (http://www.ncbi.nlm.nih.gov/pubmed/17050517) |
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Composite Hindered and Restricted Model of Diffusion Reference: Assaf Y, Basser PJ. Composite hindered and restricted model of diffusion (CHARMED) MR imaging of the human brain. Neuroimage.2005 Aug 1;27(1) :48-58. (http://www.ncbi.nlm.nih.gov/pubmed/17050517) |
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Diffusion Orientation Transform Reference: Ozarslan E, Shepherd TM, Vemuri BC, Blackband SJ, Mareci TH. Resolution of complex tissue microarchitecture using the diffusion orientation transform (DOT). Neuroimage. 2006 Jul 1;31(3) :1086-103. Epub 2006 Mar 20. (http://www.ncbi.nlm.nih.gov/pubmed/16546404) |
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Reference: Jansons KM, Alexander DC. Persistent Angular Structure: new insights from diffusion MRI data. Dummy version. Inf Process Med Imaging.2003 Jul;18:672-83. (http://www.ncbi.nlm.nih.gov/pubmed/15344497) |
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A method to estimate the distribution of fiber orientations by deconvolution of the diffusion-weighted signal attenuation measured over the surface of a sphere expressed as the convolution over the sphere of a response function. Reference: Tournier JD, Calamante F, Gadian DG, Connelly A. Direct estimation of the fiber orientation density function from diffusion-weighted MRI data using spherical deconvolution. NeuroImage. 2004 Nov;23(3) :1176-85. (http://www.ncbi.nlm.nih.gov/pubmed/15528117) |
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The diffusion sensitization factor (b value) used during acquisition of the source image used for a diffusion model. |
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The method used to fit a set of data to a mathematical model. E.g., least squares. |
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Mono-exponential (single compartment) Apparent Diffusion Coefficient (ADC) model. |
Burdette JH, Elster AD, Ricci PE. Calculation of apparent diffusion coefficients (ADCs) in brain using two-point and six-point methods. J Comput Assist Tomogr. 1998 Oct;22(5):792-4. http://journals.lww.com/jcat/pages/articleviewer.aspx?year=1998&issue=09000&article=00023&type=abstract Toivonen J, Merisaari H, Pesola M, Taimen P, Boström PJ, Pahikkala T, et al. Mathematical models for diffusion-weighted imaging of prostate cancer using b values up to 2000 s/mm2: Correlation with Gleason score and repeatability of region of interest analysis. Magnetic Resonance in Medicine. 2015;74(4):1116-24. http://dx.doi.org/10.1002/mrm.25482 |
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Merisaari H, Movahedi P, Perez IM, Toivonen J, Pesola M, Taimen P, et al. Fitting methods for intravoxel incoherent motion imaging of prostate cancer on region of interest level: Repeatability and gleason score prediction. Magnetic Resonance in Medicine. 2016. http://dx.doi.org/10.1002/mrm.26169 Toivonen J, Merisaari H, Pesola M, Taimen P, Boström PJ, Pahikkala T, et al. Mathematical models for diffusion-weighted imaging of prostate cancer using b values up to 2000 s/mm2: Correlation with Gleason score and repeatability of region of interest analysis. Magnetic Resonance in Medicine. 2015;74(4):1116-24. http://dx.doi.org/10.1002/mrm.25482 Barbieri S, Donati OF, Froehlich JM, Thoeny HC. Impact of the calculation algorithm on biexponential fitting of diffusion-weighted MRI in upper abdominal organs. Magnetic Resonance in Medicine. 2016;75(5):2175-84. http://dx.doi.org/10.1002/mrm.25765 |
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Toivonen J, Merisaari H, Pesola M, Taimen P, Boström PJ, Pahikkala T, et al. Mathematical models for diffusion-weighted imaging of prostate cancer using b values up to 2000 s/mm2: Correlation with Gleason score and repeatability of region of interest analysis. Magnetic Resonance in Medicine. 2015;74(4):1116-24. http://dx.doi.org/10.1002/mrm.25482 |
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Oshio K, Shinmoto H, Mulkern RV. Interpretation of diffusion MR imaging data using a gamma distribution model. Magn Reson Med Sci. 2014;13: 191-195. http://dx.doi.org/10.2463/mrms.2014-0016 |
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Bennett KM, Schmainda KM, Bennett RT, Rowe DB, Lu H, Hyde JS. Characterization of continuously distributed cortical water diffusion rates with a stretched-exponential model. Magn Reson Med. 2003;50: 727-734. http://dx.doi.org/10.1002/mrm.10581 Toivonen J, Merisaari H, Pesola M, Taimen P, Boström PJ, Pahikkala T, et al. Mathematical models for diffusion-weighted imaging of prostate cancer using b values up to 2000 s/mm2: Correlation with Gleason score and repeatability of region of interest analysis. Magnetic Resonance in Medicine. 2015;74(4):1116-24. http://dx.doi.org/10.1002/mrm.25482 |
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Yablonskiy DA, Bretthorst GL, Ackerman JJH. Statistical model for diffusion attenuated MR signal. Magnetic Resonance in Medicine. 2003;50(4):664-9. http://dx.doi.org/10.1002/mrm.10578 |
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Model fitting by using the log of the ratio of the two samples. |
Burdette JH, Elster AD, Ricci PE. Calculation of apparent diffusion coefficients (ADCs) in brain using two-point and six-point methods. J Comput Assist Tomogr. 1998 Oct;22(5):792-4. http://journals.lww.com/jcat/pages/articleviewer.aspx?year=1998&issue=09000&article=00023&type=abstract |
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Model fitting by least squares method from more than two samples. |
Burdette JH, Elster AD, Ricci PE. Calculation of apparent diffusion coefficients (ADCs) in brain using two-point and six-point methods. J Comput Assist Tomogr. 1998 Oct;22(5):792-4. http://journals.lww.com/jcat/pages/articleviewer.aspx?year=1998&issue=09000&article=00023&type=abstract |
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Barbieri S, Donati OF, Froehlich JM, Thoeny HC. Impact of the calculation algorithm on biexponential fitting of diffusion-weighted MRI in upper abdominal organs. Magnetic Resonance in Medicine. 2016;75(5):2175-84. http://dx.doi.org/10.1002/mrm.25765 |
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Barbieri S, Donati OF, Froehlich JM, Thoeny HC. Impact of the calculation algorithm on biexponential fitting of diffusion-weighted MRI in upper abdominal organs. Magnetic Resonance in Medicine. 2016;75(5):2175-84. http://dx.doi.org/10.1002/mrm.25765 |
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Barbieri S, Donati OF, Froehlich JM, Thoeny HC. Impact of the calculation algorithm on biexponential fitting of diffusion-weighted MRI in upper abdominal organs. Magnetic Resonance in Medicine. 2016;75(5):2175-84. http://dx.doi.org/10.1002/mrm.25765 |
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Barbieri S, Donati OF, Froehlich JM, Thoeny HC. Impact of the calculation algorithm on biexponential fitting of diffusion-weighted MRI in upper abdominal organs. Magnetic Resonance in Medicine. 2016;75(5):2175-84. http://dx.doi.org/10.1002/mrm.25765 |
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Barbieri S, Donati OF, Froehlich JM, Thoeny HC. Impact of the calculation algorithm on biexponential fitting of diffusion-weighted MRI in upper abdominal organs. Magnetic Resonance in Medicine. 2016;75(5):2175-84. http://dx.doi.org/10.1002/mrm.25765 |
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Barbieri S, Donati OF, Froehlich JM, Thoeny HC. Impact of the calculation algorithm on biexponential fitting of diffusion-weighted MRI in upper abdominal organs. Magnetic Resonance in Medicine. 2016;75(5):2175-84. http://dx.doi.org/10.1002/mrm.25765 Neil JJ, Bretthorst GL. On the use of bayesian probability theory for analysis of exponential decay date: An example taken from intravoxel incoherent motion experiments. Magnetic Resonance in Medicine. 1993;29(5):642-7. http://dx.doi.org/10.1002/mrm.1910290510 |
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Gatidis S, Schmidt H, Martirosian P, Nikolaou K, Schwenzer NF. Apparent diffusion coefficient-dependent voxelwise computed diffusion-weighted imaging: An approach for improving SNR and reducing T2 shine-through effects. Journal of Magnetic Resonance Imaging. 2016;43(4):824-32. http://dx.doi.org/10.1002/jmri.25044 |
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Coefficient reflecting the anisotropy of the tissues, derived from a diffusion weighted MR image. It represents the volume of an ellipsoid whose semimajor axes are the three eigenvalues of the diffusion tensor divided by the volume of a sphere whose radius is the mean diffusivity. |
Pierpaoli C, Basser PJ. Toward a quantitative assessment of diffusion anisotropy. Magn Reson Med. 1996 Dec 1;36(6):893-906. http://onlinelibrary.wiley.com/doi/10.1002/mrm.1910360612/abstract |
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The pure diffusion coefficient, i.e., one that is not affected by T2 contrast effects. |
Graessner J. Frequently Asked Questions: Diffusion-Weighted Imaging (DWI). MAGNETOM Flash. Siemens. 2011 Jan. http://clinical-mri.com/wp-content/uploads/software_hardware_updates/Graessner.pdf |
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The diffusion coefficient of a mono-exponential diffusion model (ADCm). |
Toivonen J, Merisaari H, Pesola M, Taimen P, Boström PJ, Pahikkala T, et al. Mathematical models for diffusion-weighted imaging of prostate cancer using b values up to 2000 s/mm2: Correlation with Gleason score and repeatability of region of interest analysis. Magnetic Resonance in Medicine. 2015;74(4):1116-24. http://dx.doi.org/10.1002/mrm.25482 |
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The slow diffusion coefficient (Ds) of a bi-exponential intravoxel incoherent motion (IVIM) diffusion model. |
Merisaari H, Movahedi P, Perez IM, Toivonen J, Pesola M, Taimen P, et al. Fitting methods for intravoxel incoherent motion imaging of prostate cancer on region of interest level: Repeatability and gleason score prediction. Magnetic Resonance in Medicine. 2016. http://dx.doi.org/10.1002/mrm.26169 Toivonen J, Merisaari H, Pesola M, Taimen P, Boström PJ, Pahikkala T, et al. Mathematical models for diffusion-weighted imaging of prostate cancer using b values up to 2000 s/mm2: Correlation with Gleason score and repeatability of region of interest analysis. Magnetic Resonance in Medicine. 2015;74(4):1116-24. http://dx.doi.org/10.1002/mrm.25482 Barbieri S, Donati OF, Froehlich JM, Thoeny HC. Impact of the calculation algorithm on biexponential fitting of diffusion-weighted MRI in upper abdominal organs. Magnetic Resonance in Medicine. 2016;75(5):2175-84. http://dx.doi.org/10.1002/mrm.25765 |
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The fast diffusion coefficient (Df) of a bi-exponential intravoxel incoherent motion (IVIM) diffusion model. |
Merisaari H, Movahedi P, Perez IM, Toivonen J, Pesola M, Taimen P, et al. Fitting methods for intravoxel incoherent motion imaging of prostate cancer on region of interest level: Repeatability and gleason score prediction. Magnetic Resonance in Medicine. 2016. http://dx.doi.org/10.1002/mrm.26169 Toivonen J, Merisaari H, Pesola M, Taimen P, Boström PJ, Pahikkala T, et al. Mathematical models for diffusion-weighted imaging of prostate cancer using b values up to 2000 s/mm2: Correlation with Gleason score and repeatability of region of interest analysis. Magnetic Resonance in Medicine. 2015;74(4):1116-24. http://dx.doi.org/10.1002/mrm.25482 Barbieri S, Donati OF, Froehlich JM, Thoeny HC. Impact of the calculation algorithm on biexponential fitting of diffusion-weighted MRI in upper abdominal organs. Magnetic Resonance in Medicine. 2016;75(5):2175-84. http://dx.doi.org/10.1002/mrm.25765 |
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The fast diffusion fraction of a bi-exponential intravoxel incoherent motion (IVIM) diffusion model. |
Merisaari H, Movahedi P, Perez IM, Toivonen J, Pesola M, Taimen P, et al. Fitting methods for intravoxel incoherent motion imaging of prostate cancer on region of interest level: Repeatability and gleason score prediction. Magnetic Resonance in Medicine. 2016. http://dx.doi.org/10.1002/mrm.26169 Toivonen J, Merisaari H, Pesola M, Taimen P, Boström PJ, Pahikkala T, et al. Mathematical models for diffusion-weighted imaging of prostate cancer using b values up to 2000 s/mm2: Correlation with Gleason score and repeatability of region of interest analysis. Magnetic Resonance in Medicine. 2015;74(4):1116-24. http://dx.doi.org/10.1002/mrm.25482 Barbieri S, Donati OF, Froehlich JM, Thoeny HC. Impact of the calculation algorithm on biexponential fitting of diffusion-weighted MRI in upper abdominal organs. Magnetic Resonance in Medicine. 2016;75(5):2175-84. http://dx.doi.org/10.1002/mrm.25765 |
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The diffusion coefficient of a kurtosis diffusion model (ADCk). |
Toivonen J, Merisaari H, Pesola M, Taimen P, Boström PJ, Pahikkala T, et al. Mathematical models for diffusion-weighted imaging of prostate cancer using b values up to 2000 s/mm2: Correlation with Gleason score and repeatability of region of interest analysis. Magnetic Resonance in Medicine. 2015;74(4):1116-24. http://dx.doi.org/10.1002/mrm.25482 |
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The scale (theta) parameter of a gamma distribution diffusion model. |
Oshio K, Shinmoto H, Mulkern RV. Interpretation of diffusion MR imaging data using a gamma distribution model. Magn Reson Med Sci. 2014;13: 191-195. http://dx.doi.org/10.2463/mrms.2014-0016 |
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The shape (k) parameter of a gamma distribution diffusion model. |
Oshio K, Shinmoto H, Mulkern RV. Interpretation of diffusion MR imaging data using a gamma distribution model. Magn Reson Med Sci. 2014;13: 191-195. http://dx.doi.org/10.2463/mrms.2014-0016 |
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The mode (maximum value of probability density function) of a gamma distribution diffusion model. Computed as (k-1)*theta, for k >= 1. |
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The distributed diffusion coefficient of a stretched-exponential diffusion model (ADCs). |
Bennett KM, Schmainda KM, Bennett RT, Rowe DB, Lu H, Hyde JS. Characterization of continuously distributed cortical water diffusion rates with a stretched-exponential model. Magn Reson Med. 2003;50: 727-734. http://dx.doi.org/10.1002/mrm.10581 Toivonen J, Merisaari H, Pesola M, Taimen P, Boström PJ, Pahikkala T, et al. Mathematical models for diffusion-weighted imaging of prostate cancer using b values up to 2000 s/mm2: Correlation with Gleason score and repeatability of region of interest analysis. Magnetic Resonance in Medicine. 2015;74(4):1116-24. http://dx.doi.org/10.1002/mrm.25482 |
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The anomalous exponent (stretching, alpha) parameter of a stretched-exponential diffusion model. This describes the deviation of the signal attenuation from mono-exponential behavior |
Bennett KM, Schmainda KM, Bennett RT, Rowe DB, Lu H, Hyde JS. Characterization of continuously distributed cortical water diffusion rates with a stretched-exponential model. Magn Reson Med. 2003;50: 727-734. http://dx.doi.org/10.1002/mrm.10581 Toivonen J, Merisaari H, Pesola M, Taimen P, Boström PJ, Pahikkala T, et al. Mathematical models for diffusion-weighted imaging of prostate cancer using b values up to 2000 s/mm2: Correlation with Gleason score and repeatability of region of interest analysis. Magnetic Resonance in Medicine. 2015;74(4):1116-24. http://dx.doi.org/10.1002/mrm.25482 |
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The procedure report is a Radiopharmaceutical Radiation Dose report |
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Information pertaining to the administration of a radiopharmaceutical |
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Unique identification of a single radiopharmaceutical administration event. |
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The estimated percentage of administered activity lost at the injection site. The estimation includes extravasation, paravenous administration and leakage at the injection site. |
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The calculated activity at the Radiopharmaceutical Start Time when the radiopharmaceutical is administered to the patient. The residual activity (i.e., radiopharmaceutical not administered) , if measured, is reflected in the calculated value. The estimated extravasation is not reflected in the calculated value. |
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Radioactivity measurement of radiopharmaceutical before or during the administration. |
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Radioactivity measurement of radiopharmaceutical after the administration. |
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Registered drug establishment code for product, coding scheme example is NDC or RxNorm |
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The human readable identification of the specific radiopharmaceutical dispensed quantity or dose ("dose" as unit of medication delivery, not radiation dose measure) to be administered to the patient. |
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Identifies the vial, batch or lot number from which the individual dispense radiopharmaceutical quantity (dose) is produced. The Radiopharmaceutical Dispense Unit Identifier records the identification for each individual dose. |
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Identifies the lot or unit serial number for the reagent component for the radiopharmaceutical. |
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Identifies the lot or unit serial number for the radionuclide component for the radiopharmaceutical. |
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Information pertaining to the estimated absorbed radiation dose to an organ. |
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ICRP, 1988. Radiation Dose to Patients from Radiopharmaceuticals. ICRP Publication 53. Ann. ICRP 18 (1-4). |
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ICRP, 1998. Radiation Dose to Patients from Radiopharmaceuticals (Addendum to ICRP Publication 53). ICRP Publication 80. Ann. ICRP 28 (3). |
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ICRP, 2008. Radiation Dose to Patients from Radiopharmaceuticals - Addendum 3 to ICRP Publication 53. ICRP Publication 106. Ann. ICRP 38 (1-2). |
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Stabin MG, Sparks RB, Crowe E (1994) MIRDOSE: personal computer software for internal dose assessment in nuclear medicine [Computer program] |
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Stabin MG, Sparks RB, Crowe E (2005) OLINDA/EXM: The Second-Generation Personal Computer Software for Internal Dose Assessment in Nuclear Medicine [Computer program] |
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The reported organ dose is based on radiopharmaceutical's package insert. |
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The reported organ dose is based on Institutionally approved estimates from the Radioactive Drug Research Committee (RDRC) of the institution itself. |
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The reported organ dose is based on an Investigation new drug. |
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The device that measures the radiation activity of the radiopharmaceutical |
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The amount of fluids the patient has consumed before the procedure. |
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A description of physical activity the patient performed before the start of the procedure, such as that which may affect imaging agent biodistribution. |
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Blockage in one of the tubes (ureters) that drain urine from the kidneys |
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The patient exhibits symptoms severe of jaundice and/or has a Bilirubin >10 mg/dL. |
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Extravasation or paravenous administration of the product is visible in the images. |
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The measurement method of the Glomerular Filtration Rate is Cockroft-Gault Formula |
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The measurement method of the Glomerular Filtration Rate is CKD-EPI Formula |
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The measurement method of the Glomerular Filtration Rate is MDRD |
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The measurement method of the Glomerular Filtration Rate is non-black MDRD |
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The measurement method of the Glomerular Filtration Rate is black (MDRD) |
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The measurement method of the Glomerular Filtration Rate is female (MDRD) |
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The measurement method of the Glomerular Filtration Rate is Cystatin-based formula |
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Glomerular Filtration Rate Creatinine-based formula (Schwartz) |
The measurement method of the Glomerular Filtration Rate is Creatinine-based formula (Schwartz) |
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Small body thickness for calcium scoring adjustment. Lateral thickness is measured from skin-to-skin, at the level of the proximal ascending aorta, from an A/P localizer image. |
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Medium body thickness for calcium scoring adjustment. Lateral thickness is measured from skin-to-skin, at the level of the proximal ascending aorta, from an A/P localizer image. |
|||
Large body thickness for calcium scoring adjustment. Lateral thickness is measured from skin-to-skin, at the level of the proximal ascending aorta, from an A/P localizer image. |
|||
A number that identifies a Series. Corresponds to Series Number (0020,0011) of the PS3.3. |
|||
A number that identifies an Acquisition. Corresponds to Acquisition Number (0020,0012) of the PS3.3. |
|||
A number that identifies an Instance. Corresponds to Instance Number (0020,0013) of the PS3.3. |
|||
Acquisition where the X-Ray source does not move in relation to the patient. |
|||
Acquisition where the X-Ray source moves laterally in relation to the patient. |
|||
Acquisition where the X-Ray source moves angularly in relation to the patient. |
|||
Continuous X-Ray radiation is applied during an irradiation event. |
|||
Pulsed X-Ray radiation is applied during an irradiation event. |
|||
Filter with variation in thickness from one edge to the opposite edge. |
|||
Filter with uniform thickness that is for spectral filtering only. E.g., filter out low energy portion of the X-Ray that would only contribute to skin dose, but not to image. |
|||
A polyline defining the inner limits of a finding with fuzzy margin. |
|||
A polyline defining the outer limits of a finding with fuzzy margin. |
|||
A polyline defining the outline of the spiculations of a finding. |
|||
A polyline segment graphically indicating the location and direction of a spiculation of a finding. |
|||
A collection of points indicating the pixel locations of the spiculations of a finding. |
|||
Connected line segments indicating the center of location of a finding on an orthogonal view. |
|||
Connected line segments indicating the inner margin of the location of a finding on an orthogonal view. |
|||
Connected line segments indicating the outer location of a finding on an orthogonal view. |
|||
This procedure is intended to gather data that is used for calibration or other quality control purposes. |
|||
Retired. Replaced by (706342009, SCT, "Phantom"). |
|||
A phantom acceptable for the ACR Computed Tomography Accreditation program. |
|||
A phantom acceptable for the ACR Magnetic Resonance Imaging Accreditation program. |
|||
A phantom acceptable for the ACR Mammography Accreditation program. |
|||
A phantom acceptable for the ACR Stereotactic Breast Biopsy Accreditation program. |
|||
A phantom acceptable for the ACR SPECT Accreditation program (but not for PET). |
|||
A phantom acceptable for the ACR PET Accreditation program (but not for SPECT). |
|||
A SPECT phantom with a PET faceplate acceptable for both the ACR SPECT and PET Accreditation programs. |
|||
A PET faceplate (made to fit an existing flangeless or flanged ECT phantom) acceptable for the ACR PET Accreditation program. |
|||
A phantom used for CTDI measurement in head modes according to [IEC 60601-2-44], Ed.2.1 (Head 16 cm diameter Polymethyl methacrylate PMMA). |
|||
A phantom used for CTDI measurement in body modes according to [IEC 60601-2-44], Ed.2.1 (Body 32cm diameter Polymethyl methacrylate PMMA). |
|||
X-Ray dose data accumulated over multiple irradiation events. E.g., for a study or a performed procedure step. |
|||
Imaging using a point X-Ray source with a diverging beam projected onto a 2 dimensional detector. |
|||
Retired. Replaced by (767776000, SCT, "Niobium") |
|||
Retired. Replaced by (767775001, SCT, "Europium") |
|||
Total calculated Dose Area Product (in the scope of the including report). |
|||
Last calibration DateTime for the integrated dose meter or dose calculation. |
|||
Total Dose related to Reference Point (RP). (in the scope of the including report). |
|||
Total calculated Dose Area Product applied in Fluoroscopy Modes (in the scope of the including report). |
|||
Total calculated Dose Area Product applied in Acquisition Modes (in the scope of the including report). |
|||
Dose applied in Fluoroscopy Modes, related to Reference Point (RP). (in the scope of the including report). |
|||
Dose applied in Acquisition Modes, related to Reference Point (RP). (in the scope of the including report). |
|||
Total accumulated clock time of Fluoroscopy in the scope of the including report (i.e., the sum of the Irradiation Duration values for accumulated fluoroscopy irradiation events). |
|||
Accumulated Count of exposure pulses (single or multi-frame encoded) created from irradiation events performed with high dose (acquisition). |
|||
Applied X-Ray Tube voltage at peak of X-Ray generation, in kilovolts; Mean value if measured over multiple peaks (pulses). |
|||
Cumulative time the patient has received X-Ray exposure during the irradiation event |
Retired. Replaced by (113824, DCM, "Exposure Time"). |
||
Distance to the Reference Point (RP) defined according to IEC 60601-2-43 or equipment defined. |
|||
Positioner Primary Angle at the end of an irradiation event. For further definition see (112011, DCM, "Positioner Primary Angle"). |
|||
Positioner Secondary Angle at the end of an irradiation event. For further definition see (112012, DCM, "Positioner Secondary Angle"). |
|||
Clock time from the start of loading time of the first pulse until the loading time trailing edge of the final pulse in the same irradiation event. |
|||
Enhances or modifies the Patient orientation specified in Patient Orientation. |
|||
Orientation of the Patient with respect to the Head of the Table. |
|||
Distance from the X-Ray Source to the Equipment C-Arm Isocenter.(Center of Rotation). |
|||
Measured or calculated distance from the X-Ray source to the detector plane in the center of the beam. |
|||
Table Longitudinal Position with respect to an arbitrary reference chosen by the equipment. Table longitudinal motion is positive towards the left of the patient assuming the patient is positioned HEAD FIRST SUPINE. |
|||
Table Lateral Position with respect to an arbitrary reference chosen by the equipment. Table lateral motion is positive towards the head of the patient assuming the patient is positioned HEAD FIRST. |
|||
Table Height Position with respect to an arbitrary chosen reference by the equipment in (mm). Table motion downwards is positive. |
|||
Angle of the head-feet axis of the table in degrees relative to the horizontal plane. Positive values indicate that the head of the table is upwards. |
|||
Rotation of the table in the horizontal plane (clockwise when looking from above the table). |
|||
Angle of the left-right axis of the table in degrees relative to the horizontal plane. Positive values indicate that the left of the table is upwards. |
|||
The minimum thickness of the X-Ray absorbing material used in the filters. |
|||
Table Longitudinal Position at the end of an irradiation event; see (113751, DCM, "Table Longitudinal Position"). |
|||
Table Lateral Position at the end of an irradiation event; see (113752, DCM, "Table Lateral Position"). |
|||
Table Height Position at the end of an irradiation event; see (113753, DCM, "Table Height Position"). |
|||
Average X-Ray Tube Current averaged over time for pulse or for continuous Fluoroscopy. |
|||
Number of pulses applied by X-Ray systems during an irradiation event (acquisition run or pulsed fluoro). |
|||
Angle of the X-Ray beam in degree relative to an orthogonal axis to the detector plane. |
|||
Devices used to modify the energy or energy distribution of X-Rays. |
|||
Type of filter(s) inserted into the X-Ray beam. E.g., wedges. |
|||
The maximum thickness of the X-Ray absorbing material used in the filters. |
|||
System provided definition of the Reference Point used for Dose calculations. |
|||
Distance between the collimator blades in pixel column direction as projected at the detector plane. |
|||
Distance between the collimator blades in pixel row direction as projected at the detector plane. |
|||
Collimated field area at image receptor. Area for compatibility with IEC 60601-2-43. |
|||
Measured or calculated distance from the X-Ray source to the table plane in the center of the beam. |
|||
Effective Dose evaluation from the product of Dose Length Product (DLP) and the Effective Dose Conversion Factor (E/DLP in units of mSv/mGy-cm), where the ratio is derived by means of Monte Carlo computations. |
|||
Effective Dose evaluation from the product of the Mean CTDIfreeair and the ratio E/CTDIfreeair (mSv/mGy), where the ratio is derived by means of Monte Carlo computations. |
|||
Effective Dose evaluation from the product of Dose Length Product (DLP) and the Effective Dose Conversion Factor (E/DLP in units of mSv/mGy-cm), where the ratio is derived by means of dosimetric measurements with an anthropomorphic phantom. |
|||
Effective Dose evaluation from the product of the Mean CTDIfreeair and the ratio E/CTDIfreeair (mSv/mGy), where the ratio is derived by means of dosimetric measurements with an anthropomorphic phantom. |
|||
The CT acquisition was performed by acquiring single or multi detector data while rotating the source about the gantry while the table is not moving. Additional slices are acquired by incrementing the table position and again rotating the source about the gantry while the table is not moving. |
|||
The CT acquisition was performed by holding the source at a constant angle and moving the table to obtain a projection image. E.g., localizer. |
|||
The CT acquisition was performed by holding the table at a constant position and acquiring multiple slices over time at the same location. |
|||
The CT acquisition was performed while rotating the source about the gantry while the table movement is under direct control of a human operator or under the control of an analysis application. E.g., fluoro. |
|||
1990 Recommendations of the International Commission on Radiological Protection (ICRP Publication 60, published as the Annals of the ICRP Vol. 21, No. 1-3, Pergamon Press,1991). |
|||
Start DateTime of the first X-Ray Irradiation Event of the accumulation within a Study. |
|||
End DateTime of the last X-Ray Irradiation Event of the accumulation within a Study. |
|||
X-Ray dose accumulated over multiple CT irradiation events. E.g., for a study or a performed procedure step. |
|||
Total number of events during the defined scope of accumulation. |
|||
The total dose length product for the defined scope of accumulation. |
|||
The total Effective Dose at the defined scope of accumulation. |
|||
Identification of the reference-patient model used when Effective Dose is evaluated via Monte Carlo calculations or from a Dose Length Product conversion factor based on Monte Carlo calculations. |
|||
References the physical phantom and the type of dosimeter used when measurements are done to establish Effective Dose Conversion Factors (E/DLP) or ratios E/CTDIfreeair. |
|||
Total time the patient has received X-Ray exposure during the irradiation event. |
|||
Length of the table travel during the entire tube loading, according to [IEC 60601-2-44] |
|||
The value of the nominal width referenced to the location of the isocenter along the z axis of a single row of acquired data in mm. |
|||
The value of the nominal width referenced to the location of the isocenter along the z axis of the total collimation in mm over the area of active X-Ray detection. |
|||
For Spiral scanning: Pitch Factor = (Table Feed per Rotation (mm)) /(Nominal Total Collimation Width (mm)) For Sequenced scanning: Pitch Factor = (Table Feed per single Sequenced scan (mm)) /(Nominal Total Collimation Width (mm)). |
|||
"Mean CTDIvol" refers to the average value of the CTDIvol associated with this acquisition. |
|||
Identification, tube-potential, tube-current, and exposure-time parameters associated with an X-Ray source during an acquisition. |
|||
Identifies the particular X-Ray source (in a multi-source CT system) for which the set of X-Ray source parameter values is reported. |
|||
The exposure time for one rotation of the source around the object in s. |
|||
A label describing the type of phantom used for CTDIW measurement according to [IEC 60601-2-44] (Head 16 cm diameter PMMA, Body 32 cm diameter PMMA). |
|||
The CTDIfreeair Calculation Factor is the CTDIfreeair per mAs, expressed in units of mGy/mAs. The CTDIfreeair Calculation Factor may be used in one method calculating Dose. |
|||
The average value of the free-in-air CTDI associated with this acquisition. |
|||
Dose Length Product (DLP), expressed in mGy-cm, is an index characterizing the product of the CTDIvol and the length scanned. For Spiral scanning, DLP = CTDIvol ✕ Scanning Length. For Sequenced scanning, DLP = CTDIvol ✕ Nominal Total Collimation Width ✕ Cumulative Exposure Time / Exposure Time per Rotation. For Stationary and Free scanning, DLP = CTDIvol ✕ Nominal Total Collimation Width. |
|||
Effective Dose per DLP, reference value for Effective Dose calculation, expressed in mSv/mGY.cm. |
|||
Effective Dose Reference authority 2007 Recommendations of the International Commission on Radiological Protection (ICRP Publication 103, published as the Annals of the ICRP Vol. 37, No. 2-4, Elsevier, 2007). |
|||
The type of exposure modulation used for the purpose of limiting the dose. |
|||
Measure of the detector response to radiation in the relevant image region of an image acquired with a digital X-Ray imaging system as defined in IEC 62494-1; see PS3.3 definition of Exposure Index Macro. |
|||
The target value used to calculate the Deviation Index as defined in IEC 62494-1; see PS3.3 definition of Exposure Index Macro. |
|||
A scaled representation of the accuracy of the Exposure Index compared to the Target Exposure Index as defined in IEC 62494-1; see PS3.3 definition of Exposure Index Macro. |
|||
The clinician responsible for determining that the irradiating procedure was appropriate for the indications. |
|||
An irradiation event is the loading of X-Ray equipment caused by a single continuous actuation of the equipment's irradiation switch, from the start of the loading time of the first pulse until the loading time trailing edge of the final pulse. Any automatic on-off switching of the irradiation source during the event is not treated as separate events, rather the event includes the time between start and stop of irradiation as triggered by the user. E.g., a pulsed fluoro X-Ray acquisition shall be treated as a single irradiation event. |
|||
Retired. Replaced by (113769, DCM, "Irradiation Event UID") |
|||
Method by which dose-related details of an Irradiation Event were obtained. |
|||
Total accumulated acquisition clock time in the scope of the including report (i.e., the sum of the Irradiation Duration values for accumulated acquisition irradiation events). |
|||
Recording of data by a human operator, including manual transcription of electronic data. |
|||
15cm from the isocenter towards the X-Ray source; See IEC 60601-2-43. |
|||
30cm in front (towards the tube) of the input surface of the image receptor; See FDA Federal Performance Standard for Diagnostic X-Ray Systems §1020.32(d) (3). |
|||
1cm above the patient tabletop or cradle; See FDA Federal Performance Standard for Diagnostic X-Ray Systems §1020.32(d) (3). |
|||
30cm above the patient tabletop of cradle; See FDA Federal Performance Standard for Diagnostic X-Ray Systems §1020.32(d) (3). |
|||
15cm from the centerline of the X-Ray table and in the direction of the X-Ray source; See FDA Federal Performance Standard for Diagnostic X-Ray Systems §1020.32(d) (3). |
|||
4.2cm from the breast support surface in the direction orthogonal to the support surface. This point represents the entrance point for radiation to a standard 4.2cm thick compressed breast. See Department of Health and Human Services, Food and Drug Administration. Mammography quality standards; final rule. Federal Register. Oct. 28, 1997; 68(208):55852-55994; see 900.2(uu). |
|||
The data is copied from information present in the image Attributes. E.g., dose Attributes such as CTDIvol (0018,9345). |
|||
The data is computed from information present in the image Attributes. E.g., by using dosimetry information for the specific irradiating device make and model, applied to technique information such as KVP and mAs. |
|||
The data is derived from human-readable reports. E.g., by natural language parsing of text reports, or optical character recognition from reports saved as images by the irradiating device. |
|||
The length from which images may be reconstructed (i.e., excluding any overranging performed in a spiral acquisition that is required for data interpolation). Value is distinct from (1113825, DCM, "Scanning Length"), which is the actual length of the table travel during the entire tube loading, according to [IEC 60601-2-44], and includes overranging. Also distinct from any actual Reconstructed Volume, which may depend on the slice thickness chosen for a particular reconstruction. |
|||
The Z location that is the top (highest Z value) of the Reconstructable Volume. Specified as the Z component within the Patient Coordinate System defined by a specified Frame of Reference. |
|||
The Z location that is the bottom (lowest Z value) of the Reconstructable Volume. Specified as the Z component within the Patient Coordinate System defined by a specified Frame of Reference. |
|||
The Z location that is the top (highest Z value) of the scanning length. Specified as the Z component within the Patient Coordinate System defined by a specified Frame of Reference. |
|||
The Z location that is the bottom (lowest Z value) of the scanning length. Specified as the Z component within the Patient Coordinate System defined by a specified Frame of Reference. |
|||
The range along the z axis of the total volume irradiated, per [IEC 60601-2-44], Ed. 3, 203.115(b). The start and stop of loading corresponding to the outer edge of the full width half maximum of the free-in-air dose profile for the beam collimation used. |
|||
Report section about cumulative dose alerts during an examination. |
|||
Cumulative Dose Length Product value configured to trigger an alert; see the NEMA Dose Check Standard [NEMA XR 25-2019]. |
|||
Cumulative CTDIvol value configured to trigger an alert; see the NEMA Dose Check Standard [NEMA XR 25-2019]. |
|||
A forward estimate of the accumulated DLP plus the estimated DLP for the next Protocol Element Group; see the NEMA Dose Check Standard [NEMA XR 25-2019]. |
|||
A forward estimate at a given location of the accumulated CTDIvol plus the estimated CTDIvol for the next Protocol Element Group; see the NEMA Dose Check Standard [NEMA XR 25-2019]. |
|||
Reason provided for proceeding with a procedure that is projected to exceed a configured dose value. |
|||
Report section about dose notifications during a protocol element. |
|||
Flag denoting whether a DLP Notification Value was configured. |
|||
Flag denoting whether a CTDIvol Notification Value was configured. |
|||
Dose Length Product value configured to trigger a notification for a given protocol element. |
|||
CTDIvol value configured to trigger a notification for a given protocol element. |
|||
A forward estimate of the DLP for the next Protocol Element Group; see the NEMA Dose Check Standard [NEMA XR 25-2019]. |
|||
A forward estimate of the CTDIvol for the next Protocol Element Group; see the NEMA Dose Check Standard [NEMA XR 25-2019]. |
|||
Flag denoting whether alternative dose alert behavior has been active for CT guided interventional procedure according to the NEMA Dose Check Standard [NEMA XR 25-2019]. |
|||
The amount of ionizing radiation to which the patient was exposed. |
|||
Type, amount and route of radioactive substance administered. |
Retired. Replaced by (440252007, SCT, "Administration of radiopharmaceutical"). |
||
Exposure to ionizing radiation and associated preventive measures used to reduce the exposure of parts of the body like lead apron or eye, thyroid gland or gonad protection. |
Retired. Replaced by (73569-6, LN, "Radiation Exposure and Protection Information") |
||
The Size-Specific Dose Estimate is a patient dose estimate that takes into account the size of the patient, such as described in [AAPM Report 204] or [AAPM Report 220]. |
|||
The side-to-side (left to right) dimension of the body part being scanned (per [AAPM Report 204]). |
|||
The thickness of the body part being scanned, in the antero-posterior dimension (per [AAPM Report 204]). |
|||
The diameter of the patient at a given location along the Z-axis of the patient, assuming that the patient has a circular cross-section (per [AAPM Report 204]). |
|||
The Size Specific Dose Estimate is computed using Table 1B (32cm phantom) or Table 2B (16cm phantom) of [AAPM Report 204]. |
|||
The Size Specific Dose Estimate is computed using Table 1C (32cm phantom) or Table 2C (16cm phantom) of [AAPM Report 204]. |
|||
The Size Specific Dose Estimate is computed using Table 1A (32cm phantom) or Table 2A (16cm phantom) of [AAPM Report 204]. |
|||
The Size Specific Dose Estimate is computed using Table 1D (32cm phantom) or Table 2D (16cm phantom) using an effective diameter estimated from the patient's age using Table 3 of [AAPM Report 204]. |
|||
A segmented region of the detector surface within the irradiated area (but might not be near the center of the detector). |
|||
A device that creates digital images from X-Ray detectors (Direct, Indirect or Storage). |
|||
Parameters related to the X-Ray source (generator, tube, etc) are available to the recording application. |
|||
Parameters related to the X-Ray Mechanical System (Stand, Table) are available to the recording application. |
|||
Parameters related to the X-Ray Detector are available to the recording application. |
|||
Describes the radiographic method of patient, tube and detector positioning to achieve a well described projection or view. |
|||
Detector that directly transforms the input signal to pixel values. |
|||
Detector that transforms an intermediate signal into pixel values. E.g., a scintillator-based detector. |
|||
Storage detector that stores a signal that is later transformed by a reader into pixel values. E.g., a phosphor-based detector. |
|||
The cassette/detector is not mounted.. E.g., a cassette placed underneath the patient. |
|||
Method of mounting or positioning a CR/DR cassette or detector. |
|||
An integrated projection radiography system capable of fluoroscopy. |
|||
A projection radiography system where the X-Ray detector, X-Ray Source and gantry components are integrated and the managing system is able to access details of each component. |
|||
A projection radiography system where the X-Ray detector, X-Ray Source and gantry components are not integrated. E.g., cassette-based CR and DR systems. |
|||
Description of the algorithm used when reconstructing the image from the data acquired during the acquisition process. |
|||
An algorithm for reconstructing an image from multiple projections by back-projecting the measured values along the line of the projection and filtering the result to reduce blurring. |
|||
An algorithm for reconstructing an image from multiple projections by starting with an assumed reconstructed image, computing projections from the image, comparing the original projection data and updating the reconstructed image based upon the difference between the calculated and the actual projections. |
|||
A point at the surface of the patient within the irradiated area where the X-Ray beam enters the patient (i.e. towards the tube). |
|||
100cm from the X-Ray source along the central ray of the X-Ray beam. |
|||
The period of time from the start of a Procedure Step until the time point established by the context of the reference. |
|||
The diameter of a cylinder of water having the same X-Ray attenuation as the patient for a specified reconstructed slice (e.g., as described in [AAPM Report 220]). |
|||
The Water Equivalent Diameter is a value at a single location sufficiently representative of the body region. |
|||
The Water Equivalent Diameter integrates values for a sample of reconstructed slices across the entire scan range. |
|||
The Water Equivalent Diameter value is derived from Raw Data rather than reconstructed slices. See [AAPM Report 220]. |
|||
The Water Equivalent Diameter value is derived from a Localizer image. See [AAPM Report 220]. |
|||
Series or Instance used for Water Equivalent Diameter estimation |
Unique identifier of the Series or Instance(s) used for Water Equivalent Diameter estimation, whether it be a Series of reconstructed single slice images or one or more Enhanced Multi-frame images or a Raw Data Series or Instance. |
||
The Z location used for Water Equivalent Diameter estimation at a single location whether it be computed using a reconstructed slice or Localizer or Raw Data. Specified as the Z component within the Patient Coordinate System defined by a specified Frame of Reference. |
|||
A report describing methods of calculation of diameters of cylinders of water having the same X-Ray attenuation as reconstructed CT slices of patients described in [AAPM Report 220]. |
|||
The Size Specific Dose Estimate is calculated from a single Water Equivalent Diameter value using a conversion factor as described in [AAPM Report 204]. |
|||
The Size Specific Dose Estimate is an arithmetic average of SSDE(z), calculated from Dw(z) at several z-positions over the reconstruction length. The z-positions may or may not correspond to reconstructed slices. See [IEC 62985]. |
|||
The Water Equivalent Diameter is an arithmetic average of Dw(z) at several z-positions over the reconstruction length. The z-positions may or may not correspond to reconstructed slices. See [IEC 62985]. |
|||
The a and b coefficients of an exponential function as described in [AAPM Report 204]. The function generates a conversion factor based on a Water Equivalent Diameter value (Dw). Multiplying the Dw value by the conversion factor produces a Size Specific Dose Estimate. |
|||
The Water Equivalent Diameter is derived from reconstructed images that do not cover the full FOV. |
|||
Estimate of the average absorbed dose to the material contained in an axial plane at longitudinal position z of the object scanned. See [IEC 62985]. |
|||
The patient relative longitudinal position at which other value(s) have been estimated. |
|||
Diameter of a cylinder of water having the same averaged absorbed dose as the material contained in an axial plane at longitudinal position z of the object scanned, calculable for a material of any composition, and quantifying the attenuation of any material in terms of the attenuation of water. See [IEC 62985]. |
|||
Measurement not available: Negative Infinity (per IEEE 754). |
|||
Measurement not available: Positive Infinity (per IEEE 754). |
|||
Measures the time-of-flight of a light signal between the camera and the subject for each point of the image. |
|||
Interferometry is a family of techniques in which waves are superimposed in order to extract depth information about the scanned object. |
|||
Laser scanning describes the general method to sample or scan a surface using laser technology. |
|||
Projecting a narrow band of light onto a three-dimensionally shaped surface produces a line of illumination that appears distorted from other perspectives than that of the projector. It can be used for an exact geometric reconstruction of the surface shape. |
|||
A technique for estimating the surface normal of an object by observing that object under different lighting conditions. |
|||
A technique for estimating the surface normal of an object by observing that object under different motions. |
|||
An optical imaging technique used to increase optical resolution and contrast of a micrograph by using point illumination and a spatial pinhole to eliminate out-of-focus light in specimens that are thicker than the focal plane. It enables the reconstruction of 3D structures from the obtained images. |
|||
Scanning the object from different views by placing it on a rotating table. |
|||
An algorithm employed to minimize the difference between two clouds of points. It iteratively revises the transformation (translation, rotation) needed to minimize the distance between the points of two point clouds. |
|||
Human controlled minimization of the distance between the points of two point clouds. |
|||
Scanning the object from different views by placing it in front of a checkerboard pattern. |
|||
Type of source for observations quoted from an external source. |
|||
Organization or institution with which the human observer is affiliated for the context of the current observation. |
|||
Organizational role of human observer for the context of the current observation. |
|||
Procedural role of human observer for the context of the current observation. |
|||
Unique identifier of automated device that created the observations. |
|||
Institution-provided identifier of automated device that created the observations. |
|||
Manufacturer of automated device that created the observations. |
|||
Manufacturer-provided model name of automated device that created the observations. |
|||
Manufacturer-provided serial number of automated device that created the observations. |
|||
Location of automated device that created the observations whilst the observations were being made. |
|||
Identifier for the Order (or Service Request) assigned by the order placer system. |
|||
Identifier for the Order (or Service Request) assigned by the order filler system. |
|||
A departmental Information System generated number that identifies the Imaging Service Request. |
|||
Unique Identifier of patient or fetus who is the subject of observations. |
|||
Identifier of patient or fetus who is the subject of observations. |
|||
Name of mother of fetus that is the subject of observations. |
|||
Retired. Replaced by (11951-1, LN, "Fetus ID"). |
|||
Retired. Replaced by (55281-0, LN, "Number of Fetuses"). |
|||
Unique Identifier of specimen that is the subject of observations. |
|||
Accession Number of specimen that is the subject of observations |
|||
Coded category of specimen that is the subject of observations |
Retired. Replaced by (371439000, SCT, "Specimen Type") |
||
Identifier of specimen microscope slide that is the subject of observations |
Retired. Replaced by (111700, DCM, "Specimen Container Identifier") |
||
Unique Identifier of specimen microscope slide that is the subject of observations |
|||
The language of the content, being a language that is primarily used for human communication. E.g., English, French. |
|||
The country-specific variant of language. E.g., Canada for Candadian French. |
|||
The language of both the name component and the value component of a name-value pair. |
|||
The language of the current Content Item (node in a tree of content) and all its descendants. |
|||
A precoordinated coded concept or text meaning for the name component of a name-value pair that is equivalent to the post-coordinated meaning conveyed by the coded name and its concept modifier children. |
|||
A precoordinated coded concept or text meaning for the value component of a name-value pair that is equivalent to the post-coordinated meaning conveyed by the coded value and its concept modifier children. |
|||
Whether or not the property concept being modified is present or absent. |
|||
Retired. Replaced by (52101004, SCT, "Present") |
|||
Retired. Replaced by (272519000, SCT, "Absent") |
|||
A set of points on an image, that when connected by line segments, provide a polyline from which a linear measurement was inferred. |
|||
A set of points on an image, that when connected by line segments, provide a closed polyline that is the border of a defined region from which an area, or two-dimensional measurement, was inferred. |
|||
A set of points on an image, that when connected by line segments, provide a closed polyline that is a two-dimensional border of a three-dimensional region's intersection with, or projection into the image. |
|||
Retired. Replaced by (373068000, SCT, "Undetermined") |
|||
Retired. Replaced by (11329-0, LN, "History") |
|||
Manufacturer-provided Class UID(s) of device that created the observations. |
|||
Retired. Replaced by (55115-0, LN, "Request") |
|||
Retired. Replaced by (55111-9, LN, "Current Procedure Descriptions") |
|||
Retired. Replaced by (55114-3, LN, "Prior Procedure Descriptions") |
|||
Retired. Replaced by (18834-2, LN, "Previous Findings") |
|||
Retired. Replaced by (59776-5, LN, "Findings") |
|||
Retired. Replaced by (19005-8, LN, "Impressions") |
|||
An interpretation in the clinical context of the finding(s) on an imaging study. |
|||
Retired. Replaced by (18783-1, LN, "Recommendations") |
|||
A recommendation for management or investigation based on the findings and impressions of an imaging study. |
|||
Retired. Replaced by (55110-1, LN, "Conclusions") |
|||
An interpretation in the clinical context of the finding(s) on an imaging study. |
|||
Retired. Replaced by (55107-7, LN, "Addendum") |
|||
Initial images used to establish a beginning condition that is used for comparison over time to look for changes. [Paraphrases NCI-PT (C1442488, UMLS, "Baseline"), which is defined as "An initial measurement that is taken at an early time point to represent a beginning condition, and is used for comparison over time to look for changes. For example, the size of a tumor will be measured before treatment (baseline) and then afterwards to see if the treatment had an effect. A starting point to which things may be compared."] |
|||
A selection of composite instances that best illustrates a particular finding. E.g., an image slice at the location of the largest extent of a tumor. |
|||
Retired. Replaced by (309343006, SCT, "Physician") |
|||
Retired. Replaced by (106292003, SCT, "Nurse") |
|||
Retired. Replaced by (159016003, SCT, "Radiologic Technologist") |
|||
Retired. Replaced by (159016003, SCT, "Radiographer") |
|||
Retired. Replaced by (C1144859, UMLS, "Intern") |
|||
Retired. Replaced by (405277009, SCT, "Resident") |
|||
Retired. Replaced by (158971006, SCT, "Registrar") |
|||
A medical practitioner undergoing sub-specialty training. E.g., during the period after specialty training (residency). |
|||
Retired. Replaced by (405279007, SCT, "Attending") |
|||
Retired. Replaced by (415506007, SCT, "Scrub nurse") |
|||
Retired. Replaced by (304292004, SCT, "Surgeon") |
|||
A medical practitioner with sub-specialty training in Ultrasound. |
|||
Retired. Replaced by (C1954848, UMLS, "Sonographer") |
|||
The person responsible for referring the patient for the procedure. |
Retired. Replaced by (C1709880, UMLS, "Referring physician"). |
||
The person responsible for recording the procedure or observation. |
|||
The person responsible for verifying the recorded procedure or observation. |
|||
The person responsible for making preparations for and monitoring the procedure. |
Retired. Replaced by (413854007, SCT, "Circulating Nurse"). |
||
The person responsible for standing by to assist with the precedure if required. |
|||
Retired. Replaced by (C2985483, UMLS, "Radiation Physicist"). |
|||
Retired. Replaced by (18785-6, LN, "Indications for Procedure") |
|||
Patient condition at the beginning of a healthcare encounter |
Retired. Replaced by (55108-5, LN, "Patient Presentation") |
||
Retired. Replaced by (55112-7, LN, "Summary") |
|||
Retired. Replaced by (55109-3, LN, "Complications") |
|||
Summary of patient condition upon Discharge from a healthcare facility. |
|||
Proximal Anatomic Location for a differential measurement; may be considered subtype of term (363698007, SCT, "Finding Site"). E.g., distance or pressure gradient. |
|||
Distal Anatomic Location for a differential measurement; may be considered subtype of term (363698007, SCT, "Finding Site"). E.g., distance or pressure gradient. |
|||
Time-stamped record of events that occur during a catheterization procedure. |
|||
Concept modifier for the DateTime of Recording of an Entry in an Event Log. |
|||
Recorded DateTime had its source in a system clock not synchronized to other recorded DateTimes. |
|||
Type of device, process or method used to acquire or derive data. |
|||
Identification of a Lesion observed during an imaging procedure. |
|||
Assessment of the risk a coronary lesion presents to the health of a patient. |
|||
Action of a clinical professional at the site of percutaneous access to a patient's cardiovascular system. |
|||
The action or event of beginning circulatory support for a patient. |
|||
The action or event of ending circulatory support for a patient. |
|||
The action or event of beginning administration of oxygen to a patient. |
|||
The action or event of ending administration of oxygen to a patient. |
|||
Method of administration of oxygen to a patient by ventilator. |
|||
The action or event of assessing the clinical status of a patient. |
|||
The action or event of beginning pacing support for a patient. |
|||
The action or event of beginning ventilation support for a patient. |
|||
The action or event of ending ventilation support for a patient. |
|||
Retired. Replaced by (55113-5, LN, "Key Images") |
|||
Individual frames selected as a subset of a multi-frame image. |
|||
Segment selected as a subset of a segmentation image, specifically the pixels/voxels identified as belonging to the classification of the identified segment. |
|||
Name or other identifier of a device that is the subject of observations. |
|||
Manufacturer of a device that is the subject of observations. |
|||
Serial Number of a device that is the subject of observations. |
|||
Physical Location of a device that is the subject of observations during those observations. |
|||
Unique Identifier of a device that is the subject of observations. |
|||
Retired. Replaced by (121056, DCM, "Area Outline"). |
|||
Retired. Replaced by (131184002, SCT, "Area of defined region"). |
|||
A one dimensional, or linear, numeric measurement between two points or features. |
|||
Distance between marks on a device of calibrated size. E.g., a ruler. |
|||
Retired. Replaced by (121055, DCM, "Path"). |
|||
A one dimensional, or linear, numeric measurement along a polyline. |
|||
Retired. Replaced by (121057, DCM, "Perimeter Outline"). |
|||
Frame selected from a segmentation image, specifically the pixels/voxels identified as belonging to the classification of the segment encompassing the identified frame. |
|||
A three-dimensional numeric measurement that is approximate, based on a two-dimensional region in a single image. |
|||
A three-dimensional numeric measurement that is approximate, based on three or more non-coplanar two-dimensional image regions. |
|||
A three-dimensional numeric measurement that is approximate, based on two non-coplanar two-dimensional image regions. |
|||
A three-dimensional numeric measurement of the bounding region of a three-dimensional region of interest in an image set. |
|||
A three-dimensional numeric measurement of the bounding sphere of a three-dimensional region of interest in an image set. |
|||
A three-dimensional numeric measurement of an ellipsoid shaped three-dimensional region of interest in an image set. |
|||
A three-dimensional numeric measurement of a sphere shaped three-dimensional region of interest in an image set. |
|||
A line segment that is an arm of a pair of arms that defines an angle, whether or not those line segments share a common vertex. |
|||
The angle on an AP radiograph of the pelvis between a line drawn parallel to the acetabular roof and a line drawn horizontally through the inferior aspect of both triradiate cartilages (Hilgenreiner's line). |
|||
The approximate geometric location on an image or in space where an entity is located. |
Intended for use when it is known that the source of the information, such as a crude hand-drawn pointer, is in the neighborhood of the entity, but is not expected to be accurate. |
||
The length of that part of a line (a straight object having no curvature) that is bounded by two distinct end points and contains every point on the line between those two end points, including both of the two end points. |
Derived from https://en.wikipedia.org/wiki/Line_(geometry)#Line_segment. |
||
Series of image instances used as source data for a segmentation. |
|||
Indicates the location of the area of interest as measured from the nipple of the breast. |
|||
Indicates the location of the area of interest as measured from the most direct skin point of the breast. |
|||
Indicates the location of the area of interest as measured from the chest wall. |
|||
The act of communicating actionable findings to a responsible receiver. |
|||
Reference is to a Doppler waveform acquired simultaneously with an image. |
|||
Reference is to a Hemodynamic waveform acquired simultaneously with an image. |
|||
Reference is to a ECG waveform acquired simultaneously with an image. |
|||
Reference is to a voice narrative recording acquired simultaneously with an image. |
|||
A waveform representing chest expansion and contraction due to respiratory activity, measured simultaneously with the acquisition of this Image. |
|||
Arterial pulse waveform obtained simultaneously with acquisition of a referencing image. |
|||
Phonocardiographic waveform obtained simultaneously with acquisition of a referencing image. |
|||
The referenced instance is an RT treatment plan of some type, which contains treatment positioning information, which has been verified using the information in the referencing instance. |
The referenced Instance typically will be an RT Plan, RT Ion Plan or RT Radiation Set. |
||
Image providing an anatomical reference on the patient under examination, for the purpose of defining the location of the ensuing imaging. |
|||
Image providing an anatomical reference on the patient under examination, for the purpose of planning or documenting a biopsy. |
|||
Image providing a partial view of the target anatomy, when the target anatomy is too large for a single image. |
|||
Image providing a view of the target anatomy in a different imaging plane, typically from a near perpendicular angle. |
|||
Image providing a view of the target anatomy in a different imaging plane, typically with a small angular difference. |
|||
Image where signals are identified and separated according to their frequencies. E.g., to identify individual chemicals, or individual nuclei in a chemical compound. |
|||
MR spectroscopy data acquired to correct the phase of the diagnostic data for the phase signal of the Water. |
|||
An image that has not already been lossy compressed that is used as the source for creation of a lossy compressed image. |
|||
Image used as the mask for an image processing operation, such as subtraction. |
|||
Series used as the source for an image processing operation. |
|||
SOP Instance encoded with a different SOP Class but otherwise equivalent data. |
|||
An image that has previously been lossy compressed that is used as the source for creation of another lossy compressed image. |
|||
HL7 Document Architecture (CDA) Document that contains clinical content equivalent to the referencing Instance. |
|||
Instance that contains a displayable complete rendering of the referencing Instance. |
|||
Instance that contains a displayable partial rendering of the referencing Instance. |
|||
Instance that contains a displayable complete rendering of the referencing Instance, plus additional content such as inline rendering of referenced images. |
|||
Document whose content has been wholly or partially transformed to create the referencing document. |
|||
Image providing the same view of the target anatomy acquired using only a specific imaging wavelength, frequency or energy. |
|||
Image providing an anatomical reference on the patient under examination, for the purpose of documenting the location of device such as a diagnostic or therapeutic catheter. |
|||
Image providing a graphic view of the distribution of radiation dose. |
|||
The referenced image is the source of spatially-related frames from which the referencing 3D volume data was derived. |
|||
Volume corresponding to spatially-related acquisition frames |
3D Volume containing the spatially-related frames in the referencing instance. |
||
Instance acquired prior to the referencing instance in a set of consecutively acquired instances. |
|||
Instance acquired subsequent to the referencing instance in a set of consecutively acquired instances. |
|||
Image of the same target area at lower resolution acquired in the same acquisition process. |
|||
Image of the same target area at higher resolution acquired in the same acquisition process. |
|||
Image of the same target area at different focal depth (Z-plane) acquired in the same acquisition process. |
|||
Image of the same target area at different spectral band acquired in the same acquisition process. |
|||
Source image from which FOR PRESENTATION images were created. |
|||
The reference is to a predecessor report that has been replaced by the current report. |
|||
The reference is to a predecessor report to which the current report provides an addendum. |
|||
A report that precedes the final report and may contain only limited information; it may be time sensitive, and it is not expected to contain all the reportable findings. |
|||
The dose object created was calculated by summation of existing, previously calculated, RT Dose instances. |
|||
The dose object created was calculated by summation of existing, previously calculated, RT Dose instances and dose newly calculated by the application. The newly calculated dose may or may not exist as an independent object. |
|||
An assessment of the dose delivery parameters performed before treatment. |
|||
An assessment of consistency with a previously quality-assured treatment plan performed before treatment. |
|||
The basis of the assessment was a set of rules on expected values, ranges and relationships. |
|||
The dose object created was calculated using previously calculated RT Dose Instances by taking radiobiological effects into account. |
|||
The dose object was calculated based on weighted contributions along the actual number of fractions delivered. |
|||
Concentration of the chemically or physically interesting (active) ingredient of a drug or contrast agent as delivered in product form from the manufacturer, typically in mg/ml. |
|||
X-Ray absorption of the active ingredient of a contrast agent ingredient is greater than the absorption of water (tissue). |
|||
Number of units of substance administered to a patient. E.g., tablets. |
|||
The index of the fraction of the radiotherapy plan to be delivered. |
|||
The number of fully completed radiotherapy fractions of the radiotherapy plan to be delivered. Partially completed fractions are not included. |
|||
Whether or not the patient has been checked-in, i.e., are physically present and are waiting to be called in to the treatment room. |
|||
The referenced beam number within the radiotherapy plan to be delivered. |
|||
Method of deriving or calculating a measured value. E.g., mean, or maximum of set. |
|||
Assessment of a measurement relative to a normal range of values; may be considered subtype of term (363713009, SCT, "has interpretation"). |
|||
Status of selection of a measurement for further processing or use. |
|||
Bibliographic or clinical reference for a Description of a population of measurements. |
|||
Description of a normal range of values for a measurement concept. |
|||
Bibliographic or clinical reference for a Description of a normal range of values. |
|||
Observation value selected by user for further processing or use, or as most representative. |
|||
Observation value is the recently obtained, and has been selected for further processing or use. |
|||
Observation value is the mean of several measurements, and has been selected for further processing or use. |
|||
Standard deviation of a measurement in a reference population. |
|||
Percentile Ranking of an observation value with respect a reference population. |
|||
Z-score of an observation value with respect a reference population, expressed as the dimensionless quantity (x-m) /s, where (x-m) is the deviation of the observation value (x) from the population mean (m), and s is the standard deviation of the population. |
|||
2 Sigma deviation of a measurement in a reference population. |
|||
Bibliographic reference to a formula used to compute a derived measurement; reference may be to a specific equation in a journal article. |
|||
Bibliographic reference to a Table of Values used to look up a derived measurement. |
|||
Bibliographic reference to a method used to compute a derived measurement. |
|||
Factor (divisor or multiplicand) for normalizing a measurement. E.g., body surface area used for normalizing hemodynamic measurements. |
|||
Measurement obtained by observer estimation, rather than with a measurement tool or by calculation |
Retired. Replaced by (414135002, SCT, "Estimated") |
||
Retired. Replaced by (258090004, SCT, "Calculated") |
|||
Identified issue about a state or process that has the potential to require intervention or management. |
|||
DateTime concern noted (noted by whom is determined by context of use). |
|||
Identification of a healthcare provider who performed a healthcare service; may be either a person or an organization. |
|||
Type or identifier of a medical device used on, in, or by a patient. |
|||
Cardiac stress test using pharmacologic and exercise stressors |
Retired. Replaced by (428813002, SCT, "Pharmacologic and exercise stress test") |
||
Cardiac stress test using an implanted or external cardiac pacing device |
Retired. Replaced by (428685003, SCT, "Stress test using cardiac pacing") |
||
Procedure for correction of congenital cardiovascular deformity |
Replaced by (428613004, SCT, "Correction of congenital cardiovascular deformity") |
||
Process of placing patient in the anticipated treatment position, including specification and location of positioning aids, and other treatment delivery accessories. |
|||
Acquisition of patient positioning information, using single-plane megavoltage imaging. |
|||
Acquisition of patient positioning information, using dual-plane megavoltage imaging. |
|||
Acquisition of patient positioning information, using single-plane kilovoltage imaging. |
|||
Acquisition of patient positioning information, using dual-plane kilovoltage imaging. |
|||
Acquisition of patient positioning information, using dual-plane combination kilovoltage and megavoltage imaging. |
|||
Acquisition of patient positioning information, using kilovoltage CT imaging. |
|||
Acquisition of patient positioning information, using megavoltage CT imaging. |
|||
Acquisition of patient positioning information, using optical imaging. |
|||
Acquisition of patient positioning information, using ultrasound imaging. |
|||
Acquisition of patient positioning information, using spatial fiducials. |
|||
Registration of intended and actual patient position prior to treatment delivery, using single-plane images. |
|||
Registration of intended and actual patient position prior to treatment delivery, using dual-plane images. |
|||
Registration of intended and actual patient position prior to treatment delivery, using 3D CT images and an unspecified registration approach. |
|||
Registration of intended and actual patient position prior to treatment delivery, using 3D CT images and a marker-based registration approach. |
|||
Registration of intended and actual patient position prior to treatment delivery, using 3D CT images and a volume-based registration approach. |
|||
Registration of intended and actual patient position prior to treatment delivery, using 3D verification images and 2D reference images. |
|||
Registration of intended and actual patient position prior to treatment delivery, using 2D verification images and 3D reference images. |
|||
Registration of intended and actual patient position prior to treatment delivery, using optical images. |
|||
Registration of intended and actual patient position prior to treatment delivery, using ultrasound images. |
|||
Registration of intended and actual patient position prior to treatment delivery, using spatial fiducials. |
|||
Adjustment of patient position such that the patient is correctly positioned for treatment. |
|||
Review of patient positioning information in the process of delivering a treatment session. |
|||
Simulated radiotherapy treatment delivery using verification integral to the Treatment Delivery System. |
|||
Simulated radiotherapy treatment delivery using verification by a external Machine Parameter Verifier. |
|||
Radiotherapy treatment delivery using verification integral to the Treatment Delivery System. |
|||
Radiotherapy treatment delivery using verification by a external Machine Parameter Verifier. |
|||
Quality assurance of a radiotherapy treatment delivery using verification integral to the Treatment Delivery System. |
|||
Quality assurance of a radiotherapy treatment delivery using verification by a external Machine Parameter Verifier. |
|||
Perform Quality Assurance on an RT Plan by evaluating dosimetric content of the current RT Plan. |
|||
Perform Quality Assurance on an RT Plan by comparing the content of previously quality-assessed RT Plans with the current RT Plan. |
|||
Perform Quality Assurance on an RT Ion Plan by evaluating dosimetric content of the current RT Ion Plan. |
|||
Perform Quality Assurance on an RT Ion Plan by comparing the content of previously quality-assessed RT Ion Plans by the current RT Ion Plan. |
|||
Radiotherapy image-guided patient positioning and treatment delivery using verification integral to the Treatment Delivery System. |
|||
Acquisition of radiotherapy patient positioning information, using magnetic resonance imaging. |
|||
Registration of intended and actual patient position prior to treatment delivery, using MR images and an unspecified registration approach. |
|||
Indicates whether the treatment to be delivered is a complete fraction or a continuation of previous incompletely treated fraction. |
|||
Retired. Replaced by (110501, DCM, "Equipment failure") |
|||
Retired. Replaced by (429163003, SCT, "15-Lead ECG") |
|||
Analysis or measurements for current procedure (purpose of reference to evidence document). |
|||
Identifier of consumable whose remaining content has been disposed. |
|||
Identifier of Contrast agent whose administration has started. |
|||
Identifier of Contrast agent whose administration has ended. |
|||
Action of a clinical professional performed on a patient for therapeutic purpose. |
|||
Undiluted dose of Drug, Contrast agent, or Infusate administered. |
|||
Concentration of Drug, Contrast agent, or Infusate administered. |
|||
Duration of Drug, Contrast agent, or Infusate administration. |
|||
Volume of Drug, Contrast agent, or Infusate unadministered or discarded. |
|||
Measured change of patient electrocardiographic ST level relative to baseline measurement. |
|||
Anatomic term modifier indicating aneurysm on cited vessel is the subject of the finding. |
|||
Anatomic term modifier indicating proximal section of graft to cited vessel is the subject of the finding. |
|||
Anatomic term modifier indicating mid section of graft to cited vessel is the subject of the finding. |
|||
Anatomic term modifier indicating distal section of graft to cited vessel is the subject of the finding. |
|||
Lesion stenosis measured prior to any interventional procedure |
Retired. Replaced by (408715008, SCT, "Lumen Diameter Stenosis"), post-coordinated with (128955008, SCT, "Baseline Phase") |
||
Retired. Replaced by (408715008, SCT, "Lumen Diameter Stenosis"), post-coordinated with (128960007, SCT, "Post-intervention Phase") |
|||
Assessment of perfusion across a coronary lesion measured prior to any interventional procedure. |
|||
Assessment of perfusion across a coronary lesion measured after an interventional procedure. |
|||
Indication that device is the primary (first and/or most significant) device used for interventional therapy of a particular pathology. E.g., lesion. |
|||
Indication that the procedure includes a percutaneous coronary intervention. |
|||
Lesion Morphology; form and/or structural properties of lesion. |
|||
Vessel Morphology; form and/or structural properties of vessel. |
|||
Technique (device or procedure) of support for patient circulatory system; hemodynamic support. |
|||
Indication that the current study data has been compared with prior study data. |
|||
The date and time on which a procedure was performed on a patient. |
|||
Beat Number; ordinal of cardiac cycle within an acquisition. |
|||
Complex coded semantic unit, consisting of several coded components. |
|||
Trend (temporal progression) of a clinical condition, finding, or disease. |
|||
Derived cross-sectional area of a vessel or anatomic feature, other than a cardiac valve. |
|||
Indication that a Coronary Artery Bypass operation was performed during the current hospital admission. |
|||
Indication that the patient died during the current hospital admission. |
|||
Indication that the patient died during the current Catheterization procedure. |
|||
Finding of Acute Myocardial Infarction Presence as indication for interventional procedure. |
|||
DateTime of first determination of elevated ECG ST segment, as indication of Myocardial Infarction. |
|||
Number of lesion interventions attempted during current procedure. |
|||
Number of lesion interventions successful during current procedure, where the residual post intervention stenosis is less than or equal to 50% of the arterial luminal diameter, TIMI Flow is 3 and the minimal decrease in stenosis was 20%. |
|||
Indication that Myocardial Infarction occurred during current procedure. |
|||
Time interval between ECG R-wave peaks in subsequent cardiac cycles. |
|||
Elapsed time from injection of an indicator bolus until it is observed at another location. |
|||
The secondary peak pressure in the atrium during atrial contraction. |
|||
Venous or atrial pressure minimum during ventricular systole, after A-wave. |
|||
Venous or atrial pressure minimum when tricuspid valve opens during diastole, after V-wave. |
|||
Atrial pressure upon closure of tricuspid and mitral valves. |
|||
Body Surface Area computed from patient height and weight: BSA = 0.003207*WT[g]^(0.7285-0.0188*log(WT[g]))*HT[cm]^0.3 [Boyd E, The growth of the surface area of the human body. Minneapolis: University of Minnesota Press, 1935, eq. (36) ]. |
|||
Body Surface Area computed from patient height and weight: BSA = 0.007184*WT[kg]^0.425*HT[cm]^0.725 [Dubois and Dubois, Arch Int Med 1916 17:863-71]. |
|||
Body Surface Area computed from patient height and weight: BSA = 0.0235*WT[kg]^0.51456*HT[cm]^0.42246 [Gehan EA, George SL, 'Estimation of human body surface area from height and weight', Cancer Chemother Rep 1970 54:225-35]. |
|||
Body Surface Area computed from patient height and weight: BSA = 0.024265*WT[kg]^0.5378*HT[cm]^0.3964 [Haycock G.B., Schwartz G.J., Wisotsky D.H. 'Geometric method for measuring body surface area: A height weight formula validated in infants, children and adults.' The Journal of Pediatrics 1978 93:1:62-66]. |
|||
Body Surface Area computed from patient height and weight: BSA = (HT[m]*WT[kg]/36)^0.5 [Mosteller, R.D. 'Simplified Calculation of Body Surface Area.' N Engl J Med 1987 Oct 22;317(17):1098]. |
|||
Body Surface Area computed from patient weight:BSA = 1321 + 0.3433 * WT[kg] (for pediatrics 3-30 kg) [Current, J.D. 'A Linear Equation For Estimating The Body Surface Area In Infants And Children', The Internet Journal of Anesthesiology. 1998. 2:2]. |
|||
BSA = 0.0004688*(1000*WT)^(0.8168-0.0154*log(1000*WT)) Where (WT is weight in kilogram) Boyd, Edith. The Growth of the Surface Area of the Human Body(originally published in 1935 by the University of Minnesota Press), Greenwood Press, Westport, Connecticut, 1975, p. 102.Equation (35). |
|||
Equation for estimated oxygen consumption: VO2male = BSA (138.1 - 11.49 * loge(age) + 0.378 * HRf). |
|||
Equation for estimated oxygen consumption: VO2female = BSA (138.1 - 17.04 * loge(age) + 0.378 * HRf). |
|||
Equation for estimated oxygen consumption: VO2 = VeSTPD * 10 * (FIO2 - FE02). |
|||
Estimate of Oxygen partial pressure at 50% saturation for premature infants less than 3 days old: P50 = 19.9. |
|||
Estimate of Oxygen partial pressure at 50% saturation for infants less than 1 day old: P50 = 21.6. |
|||
Estimate of Oxygen partial pressure at 50% saturation for infants less than 30 days old: P50 = 24.6. |
|||
Estimate of Oxygen partial pressure at 50% saturation for patients less than 18 years old: P50 = 27.2. |
|||
Estimate of Oxygen partial pressure at 50% saturation for patients less than 40 years old: P50 = 27.4. |
|||
Estimate of Oxygen partial pressure at 50% saturation for patients more than 60 years old: P50 = 29.3. |
|||
Cardiac valve area computed from flow and pressure gradient: Area = Flow / 44.5 * sqrt(Gradient[mmHg]) [Gorlin and Gorlin, Am Heart J, 1951]. |
|||
Mitral valve area computed from flow and pressure gradient: Mitral valve Area = Flow / 38.0 * sqrt(Gradient[mmHg]) [Gorlin and Gorlin, Am Heart J, 1951]. |
|||
Body Mass Index computed from weight and height: BMI = Wt/Ht^2. |
|||
Body Surface Area computed from patient height and weight: BSA = 0.007358*WT[kg]^0.425*HT[cm]^0.725 (for East Asian adult, aged 15+ years) [Kanai Izumi, Masamitsu Kanai, 'Clinical examination method summary']. |
|||
Body Surface Area computed from patient height and weight: BSA = 0.010265*WT[kg]^0.423*HT[cm]^0.651 (For East Asian child aged 12-14 years). |
|||
Body Surface Area computed from patient height and weight: BSA = 0.008883*WT[kg]^0.444*HT[cm]^0.663 (For East Asian child aged 6-11 years). |
|||
Body Surface Area computed from patient height and weight: BSA = 0.038189*WT[kg]^0.423*HT[cm]^0.362 (For East Asian child aged 1-5 years). |
|||
Body Surface Area computed from patient height and weight: BSA = 0.009568*WT[kg]^0.473*HT[cm]^0.655 (For East Asian child aged 0-12 months). |
|||
Anatomy could not be visualized for the purpose of evaluation. |
|||
Factor by which a measured or calculated value is multiplied to obtain the estimated real-world value. |
|||
External Elastic Membrane (EEM) diameter measured through the center point of the vessel. Center point of the vessel is defined as the center of gravity of the EEM area. The EEM is a discrete interface at the border between the media and the adventitia. |
|||
The distance from intimal leading edge to the external elastic membrane along any line passing through the luminal center, which is defined as the center of gravity of the lumen area. |
|||
Vessel area measured at the External Elastic Membrane (EEM), a discrete interface at the border between the media and the adventitia. |
|||
Area within the EEM occupied by atheroma, regardless of lumen compromise. Plaque plus Media Area = EEM cross-sectional area - vessel lumen cross-sectional area. |
|||
Measurement of in-stent restenosis. In-Stent Intimal Area = Stent cross-sectional area - vessel lumen cross-sectional area. |
|||
Longitudinal extent of the Vascular Volume Measurement. This is the distance from the distal edge to the proximal edge of the Volume measurement. |
|||
Longitudinal distance from the closest edge of a fiducial feature or reference location to the start of the vascular measurement. This value will be a positive if the measurement is distal to the fiducial feature or reference location, or negative if the measurement is proximal to the fiducial feature or reference location. |
|||
Reference, normally anatomical, which is used for locating the position of a measurement. |
|||
Measurement of vessel lumen eccentricity. Lumen Eccentricity Index = (maximum vessel lumen diameter - minimum vessel lumen diameter) / maximum vessel lumen diameter. Lumen diameters are measured through the center point of the lumen, which is defined as the center of gravity of the lumen area. |
|||
Plaque plus Media Eccentricity Index = (maximum Plaque plus media thickness - minimum Plaque plus media thickness) / maximum Plaque plus media thickness. |
|||
Measurement of increase or decrease in EEM area that occurs during the development of atherosclerosis. Remodeling Index = Lesion EEM area / reference EEM area. |
|||
Measurement of stent circularity. Stent Symmetry Index = (maximum stent diameter - minimum stent diameter) / maximum stent diameter. |
|||
Measurement of stent area relative to the reference lumen area. Stent Expansion Index = Minimum stent area / reference vessel lumen cross-sectional area. |
|||
Measurement of vessel lumen eccentricity. Lumen Shape Index = (2p * sqrt(Vessel lumen cross-sectional area / p) / Lumen Perimeter) 2 Reference: Tobis & Yock, "Intravascular Ultrasound Imaging", Chapter 7. |
|||
Lumen diameter ratio = minimum vessel lumen diameter / maximum vessel lumen diameter, measured at the same cross section in the vessel. Lumen diameters are measured through the center point of the lumen, which is defined as the center of gravity of the lumen area. |
|||
Stent diameter ratio = Minimum stent diameter / Maximum stent diameter, measured at the same cross section in the vessel. Stent diameters are measured through the center point of the stent, which is defined as the center of gravity of the stent area. |
|||
EEM diameter ratio = minimum EEM diameter / maximum EEM diameter. Measured at the same cross section in the vessel. |
|||
Fractional area within the External Elastic Membrane (EEM) occupied by atheroma. Plaque Burden = (EEM area - vessel lumen cross-sectional area) / EEM area. |
|||
Angular measurement of a Calcium deposit with the apex located at the center of the lumen, which is defined as the center of gravity of the lumen area. |
|||
Abnormal thickening of the intima within the stented segment. |
|||
Lumen surrounded by all three layers of the vessel-intima, media, and adventitia. |
|||
A channel, usually parallel to the true lumen, which does not communicate with the true lumen over a portion of its length. |
|||
Worst stenosis - the stenosis with the smallest lumen size within a vessel segment. |
|||
External Elastic Membrane (EEM) volume measured within a specified region. The EEM is a discrete interface at the border between the media and the Adventitia. |
|||
The amount of plaque between the lumen and stent, within the stent region; In-stent restenosis. In-Stent Neointimal Volume = Stent Volume - Lumen Volume. |
|||
The amount of plaque between the stent and the EEM, within the stent region. Native Plaque Volume = EEM Volume - Stent Volume. |
|||
Total amount of plaque between the EEM and the Lumen, over the entire region that is measured. Total Plaque Volume = EEM Volume - Lumen Volume. |
|||
Proximal reference segment measurement site. Typically the site with the largest lumen proximal to a stenosis but within the same segment (usually within 10 mm of the stenosis with no major intervening branches). |
|||
Distal reference segment measurement site. Typically the site with the largest lumen distal to a stenosis but within the same segment (usually within 10 mm of the stenosis with no major intervening branches). |
|||
Site of the smallest lumen in a vessel. E.g., due to a stenotic lesion. |
|||
Measurement region that encompasses the entire vessel imaged in a single pullback acquisition. |
|||
Region starting at the proximal edge of the Stent and extending several millimeters (usually 5 mm) proximal to the Stent edge. |
|||
Region starting at the distal edge of the Stent and extending several millimeters (usually 5 mm) distal to the Stent edge. |
|||
Separation of neointimal hyperplasia from stent struts, usually seen only after treatment of in-stent restenosis. |
|||
Plaque with a thin cap fibrous atheroma that is at increased risk of rupture and thrombosis (or re-thrombosis) and rapid stenosis progression. |
|||
Plaque erosions with no structural defect (beyond endothelial injury) or gap in the plaque. |
|||
Stenosis severity classifications of multiple lesions in a vessel. |
|||
A finding of a previously treated lesion in which stenosis has reoccurred. |
|||
Loosely packed bundles of collagen fibers with regions of lipid deposition present. Region is cellular and no cholesterol clefts or necrosis are present. Some |
|||
Area within the plaque with very low echogenicity separated from the lumen and surrounded by more echogenic structures (fibrous cap). Highly lipidic necrotic region with remnants of foam cells and dead lymphocytes present. No collagen fibers are visible and mechanical integrity is poor. Cholesterol clefts and micro calcifications are visible. |
|||
Separation of the layers of an artery involving the adventitia |
|||
Separation of the layers of an artery involving the intima. Dissection limited to the intima or atheroma, and not extending to the media. |
|||
Separation of the layers of an artery involving the media. Dissection in the arterial Media, extending into the media. |
|||
The referenced information was acquired simultaneously with the information in the object in which the reference occurs. |
|||
Information acquired for the same indication. E.g., to elucidate the same diagnostic question. |
|||
The referenced information was used to correct the data for differential attenuation through different anatomic tissue. |
|||
Contour repositioning of End Diastolic relative to End Systolic contour. |
|||
The minimum standard deviation to define the hypokinesis and hyperkinesis. |
|||
Report of differentiation of wall motion compared to normal. |
|||
Relation between calculated End Diastolic volume and ventricular End Diastolic volume. The specific meaning is dependent on volume method used. |
|||
Correction factor for the calculated End Diastolic volume and ventricular End Diastolic volume. The specific meaning is dependent on volume method used. |
|||
Relation between calculated End Systolic volume and ventricular End Systolic volume. The specific meaning is dependent on volume method used. |
|||
Correction factor for the calculated End Systolic volume and ventricular End Systolic volume. The specific meaning is dependent on volume method used. |
|||
Container for spatial locations or coordinates used for calculation. |
|||
The length between End Diastolic and End Systolic contour perpendicular on the centerline normalized by a method dependent ventricular perimeter length. The centerline is the line equidistant between the End Diastolic and End Systolic contour [example: Sheehan, 1986]. |
|||
The report of the boundaries of the abnormal (hyperkinetic, hypokinetic, a-kinetic) regions associated with the territory of the artery [example: Sheehan, 1986]. |
|||
The chord number specifying the begin of abnormal region [example: Sheehan, 1986]. |
|||
The chord number specifying the end of abnormal region [example: Sheehan, 1986]. |
|||
Severity at the regional abnormality extent [example: Sheehan, 1986]. |
|||
Severity at the opposite regional abnormality extent [example: Sheehan, 1986]. |
|||
Based on a total number of chords of 100 and RAO project the range of chords belonging to this circumferential extent lies between 5 - 85. [Sheehan, 1986]. |
|||
Based on a total number of chords of 100 and RAO project the range of chords belonging to this circumferential extent lies between 25 - 85. [Sheehan, 1986]. |
|||
Based on a total number of chords of 100 and RAO projection the range of chords belonging to this regional extent lies between 10 - 66 (hypokinetic) and 67 - 80 (hyperkinetic). [Sheehan, 1986]. |
|||
Based on a total number of chords of 100 and RAO projection the range of chords belonging to this regional extent lies between 51 - 80 (hypokinetic) and 10 - 50 (hyperkinetic). [Sheehan, 1986]. |
|||
Based on a total number of chords of 100 and RAO projection the range of chords belonging to this regional extent lies between 10 - 58 (hypokinetic) and 59 -80 (hyperkinetic). [Sheehan, 1986]. |
|||
Based on a total number of chords of 100 and RAO projection the range of chords belonging to this regional extent lies between 59 - 80 (hypokinetic) and 10 - 58 (hyperkinetic). [Sheehan, 1986]. |
|||
Based on a total number of chords of 100 and LAO projection the range of chords belonging to this regional extent lies between 50 -100 (hypokinetic) and 20 - 49 (hyperkinetic). [Sheehan, 1986]. |
|||
Based on a total number of chords of 100 and LAO projection the range of chords belonging to this regional extent lies between 19 - 67 (hypokinetic) and 68 - 100 (hyperkinetic). [Sheehan, 1986]. |
|||
Based on a total number of chords of 100 and LAO projection the range of chords belonging to this regional extent lies between 38 -74 (hypokinetic) and 75 - 100 (hyperkinetic). [Sheehan, 1986]. |
|||
Method based on assumption that the image object is circular. |
|||
End Systolic contour realigned to End Diastolic contour based on the center of gravity. |
|||
End Systolic contour realigned to End Diastolic contour based on the mid point of the long axis. The long axis end points are defined as the posterior and apex. |
|||
Calculated Vessel Lumen Cross-Sectional Area based on the referenced method. |
|||
Sphere visible in an image, which is used as a calibration or marker object. |
|||
Object of interest in isocenter of image and pixel separation is calculated from geometric data. |
|||
Object of interest not in isocenter of image and pixel separation is calculated from geometric data and out of isocenter distances. |
|||
Application dependent method to calculate the reference diameter based on the multiple diameter values. |
|||
Application dependent method to calculate reference by interpolation, based on the diameter of two or more user defined reference positions. |
|||
Application dependent method to calculate by averaging the reference, based on the diameter of one or more user defined reference positions. |
|||
Method to calculate wall motion based on the lengths of the radials in the predefined regions [Ingels]. |
|||
Contribution of Region to global Ejection factor based on radial or landmark based wall motion method. |
|||
The reduction of area between End Systolic and End Diastolic based on radial wall motion analysis. |
|||
Method to calculate wall motion based on the move of landmarks on the wall [Slager]. |
|||
Contribution to the ejection fraction of a specific slice region [Slager]. |
|||
Method to calculate volumes of heart chambers for every image in a range. |
|||
The area is derived by considering a set of coordinates as a closed irregular polygon, accounting for inner angles. The exact method, such as by decomposition into triangles or quadrilaterals, is not specified, since it does not affect the numeric result, apart from the effect of numeric precision during computation of intermediate results. |
|||
The area is derived by using a set of coordinates as control points for a Non Uniform Rational B-Spline (NURBS). |
|||
Integration of sum of closed areas on contiguous slices method for volume |
Method of integrating the sum of the areas on adjacent slices across the slice interval to derive a total volume; each area is defined by a regular planar shape or by considering a set of coordinates as a closed irregular polygon, accounting for inner angles. |
||
Procedure used to calibrate measurements or measurement devices. |
|||
Ordered set of diameters values derived from contours (direction proximal to distal). |
|||
Ordered set of cross-sectional Vessel Lumen Cross-Sectional Area values derived from contours (direction proximal to distal) based on densitometric method. |
|||
Position of proximal border of segment relative to the contour start (proximal end of analysis area). |
|||
Position of distal border of segment relative to the contour start (proximal end of analysis area). |
|||
Symmetry of stenosis (0 = complete asymmetry, 1 = complete symmetry); see Section T.2 “Definition of Diameter Symmetry with Arterial Plaques” in PS3.17 . |
|||
Symmetry of plaque (0 = complete asymmetry, 1 = complete symmetry); see Section T.2 “Definition of Diameter Symmetry with Arterial Plaques” in PS3.17 . |
|||
The average slope of the diameter function between the position of the minimum luminal diameter and the position of the proximal border of the segment. |
|||
The average slope of the diameter function between the position of the minimum luminal diameter and the position of the distal border of the segment. |
|||
Estimate of the volume of blood flow in the absence of stenosis. |
|||
Corrected Body Surface area for indexing the hemodynamic measurements for a pediatric patient. |
|||
Method for selecting sub-segments that are all of the same length. |
|||
Report of a Cardiovascular Analysis, typically from a CT or MR study. |
|||
Section Heading for absolute values of ventricular measurements. |
|||
Central breathing position between inspiration and expiration. |
|||
Time interval until time of peak filling from a given reference point. E.g., end systole. |
|||
The ratio of the end-systolic wall thickness compared to the end-diastolic wall thickness. |
|||
The method to smooth a ventricular volume as a function of time. |
|||
The time in a dynamic set of images at which the first peak of the signal is observed for the analyzed myocardial wall segments. |
|||
Time interval between the beginning of the signal increase to the time at which the signal intensity reaches its first maximum in a dynamic set of images. |
|||
Signal intensity as a function of time. It is the change in the signal intensity divided by the change in the time. |
|||
MR perfusion time integral from baseline (foot time) to earliest peak. |
|||
First time point in a dynamic set of images used in the calculation of the baseline signal intensity for each myocardial wall segment. |
|||
Last time point in a dynamic set of images used in the calculation of the baseline signal intensity for each myocardial wall segment. |
|||
The minimum velocity encoded by the phase encoding gradient. |
|||
The maximum velocity encoded by the phase encoding gradient. |
|||
Diameter Based Method for estimating volume, area or diameter. |
|||
A method of diameter measurements according to NASCET (North American Symptomatic Carotid Endarterectomy Trial). |
|||
A method of diameter measurements according to ECST (European Carotid Surgery Trial). |
|||
Delayed hyperenhancement of a tissue observed in an image acquired after injection of contrast media. |
|||
Relationship between blood velocity and time relative to R-wave peak. |
|||
Indicates if the papillary muscle was included or excluded in the measurement. |
|||
Finding about the characteristics of the parent vessel of a vessel. |
|||
The physical domain (time, space, etc.) to the horizontal axis of the graphical presentation. |
|||
The physical domain (time, space, etc.) to the vertical axis of the graphical presentation. |
|||
Reference time for measurement of elapsed time in a procedure. |
|||
Peak physical activity intensity measurement during course of procedure. |
|||
Ordered subsets expectation maximization reconstruction algorithm. |
|||
Attenuation correction not based on image-based attenuation maps. |
|||
Bazett QT Correction Algorithm; QT/(RR ^ 0.5); Bazett HC. "An analysis of the time-relations of electrocardiograms" Heart7:353-370 (1920). |
|||
Hodges QT Correction Algorithm; QT + 1.75 (heart rate-60); Hodges M, Salerno Q, Erlien D. "Bazett's QT correction reviewed. Evidence that a linear QT correction for heart rate is better." J Am Coll Cardiol1:694 (1983). |
|||
Fridericia QT Correction Algorithm; QT/(RR ^ 0.333); Fridericia LS. "The duration of systole in the electrocardiogram of normal subjects and of patients with heart disease" Acta Med Scand53:469-486 (1920). |
|||
Framingham QT Correction Algorithm; QT + 0.154 (1- RR); Sagie A, Larson MG, Goldberg RJ, et al. "An improved method for adjusting the QT interval for heart rate (the Framingham Heart Study)." Am J Cardiol70:797-801(1992). |
|||
Borg category ratio scale, open ended range with nominal range 0:10. |
|||
Quality of a study for the purpose for which it was created. |
|||
Quality of an image is excellent for the purpose for which it was created. |
|||
Quality of an image is good for the purpose for which it was created. |
|||
Quality of an image is poor for the purpose for which it was created. |
|||
Finding of a defect is incorrect. E.g., from automated analysis. |
|||
ECG is non-diagnostic due to ventricular pacing or Left Bundle Branch Block. |
|||
ECG is non-diagnostic for presence of acute coronary syndrome. |
|||
Workload (Watts) at target heart rate divided by body weight. |
|||
ST depression at peak exercise divided by the exercise-induced increase in heart rate [Kligfield P, Ameisen O, Okin PM. "Heart rate adjustment of ST segment depression for improved detection of coronary artery disease." Circulation 1989;79:245-55.]. |
|||
Nuclear Medicine Rest technetium/stress technetium 1 day procedure. |
|||
Nuclear Medicine Rest technetium/stress technetium 2 day procedure. |
|||
Nuclear Medicine Stress technetium/rest technetium 1 day procedure. |
|||
Positron Emission Tomography Perfusion Imaging procedure, rest only. |
|||
Positron Emission Tomography Perfusion Imaging procedure, stress only. |
|||
Positron Emission Tomography Perfusion Imaging procedure, rest and stress. |
|||
Positron Emission Tomography Myocardial Viability procedure, rest only. |
|||
Positron Emission Tomography Myocardial Viability procedure, stress only. |
|||
Positron Emission Tomography Myocardial Viability procedure, rest and stress. |
|||
Group of symptoms heralding angina pectoris that does not include chest pain (dyspnea, diaphoresis, profuse vomiting in a diabetic patient, or arm or jaw pain). |
|||
Replaced by (349358000, SCT, "Radiopharmaceutical agent"). |
|||
DateTime of radiopharmaceutical administration to the patient for imaging purposes. |
|||
Ending DateTime of radiopharmaceutical administration to the patient for imaging purposes. |
|||
Total amount of radionuclide administered to the patient at Radiopharmaceutical Start Time. |
|||
Activity per unit mass of the radiopharmaceutical at Radiopharmaceutical Start Time. |
|||
Medication to be administered at the beginning of the Scheduled Procedure Step. |
|||
Direction of imaging (includes view, transducer orientation, patient orientation, and/or projection). |
|||
Imaging condition for refinement of protocol (includes secondary posture, instruction, X-Ray / electron beam energy or nuclide, and ultrasound modes), as used in JJ1017 v3.0. |
|||
Caudal 10 degree distal-cranioproximal oblique radiographic projection, defined per Smallwood et al. |
|||
Surface processing utilizing predefined weighting factors (i.e., kernels) applied to different data values depending on their location relative to other data values within the data domain. Includes Low Pass, High Pass, Gaussian, Laplacian, etc. |
|||
Surface processing applied non-uniformly utilizing a priori knowledge of the system and/or relative locations of the data values within the data domain. Example: Neighborhood analysis where weighting factors are modified continuously based on predefined criteria. |
|||
Surface processing through the exploitation of discontinuities in the data values within their domain. Includes Gradient filters. |
|||
Surface processing based on the connectivity of values based on the shape or structure of the data values within their domain. Includes erode, dilate, etc. |
|||
Surface processing applied to the distribution of the data values. Includes thresholding, Bayesian Classification, etc. |
|||
Surface processing accomplished through varying the data domain size. Include deformable models. |
|||
Surface processing accomplished by combining data values based on their relative location within their domain or value distribution. Includes K- and C-means, Fuzzy Analysis, Watershed, Seed Growing, etc. |
|||
Surface processing accomplished through the weighted combination of multiple sets of data. Includes Principle Component Analysis, linear and non-linear weighed combinations, etc. |
|||
Surface processing accomplished through human interaction. Region drawing. |
|||
Surface processing using Artificial Intelligence techniques, such as Machine Learning, Neural Networks, etc. |
|||
Surface processing using Deformable Model techniques, such as Point Distribution Models, Level Sets, Simplex Meshes, etc. |
|||
Report section for assessment of fetal growth using ratios and indexes. |
|||
Report section for assessment of fetal growth by long bone measurements. |
|||
Report section for assessment of biophysical observations that evaluate fetal well-being according to Manning, Antepartum Fetal Evaluation: Development of a Fetal Biophysical Profile Score, Am. J Obstet Gynecol, 1980;136:787. |
|||
A grouping of related measurements and calculations that share a common context. |
|||
Report section for fetus specific procedure summary observations. |
|||
A name to differentiate between multiple instances of some item. |
|||
The rank of a measured growth indicator relative to a normal distribution expressed as a percentage. |
|||
The rank of a measured growth indicator relative to a normal distribution expressed as the dimensionless quantity z = (x-m) /s where (x-m) is the deviation of the value x, from the distribution mean, m, and s is the standard deviation of the distribution. |
|||
There is a defined equivalence between the Frame of Reference of the Registration SOP instance and the Frame of Reference of the referenced images. |
|||
The registration is based on fiducials that represent patient or specimen features identified in each set of data. |
|||
Registration based on a-priori knowledge of the acquisition geometry. This is not an object registration as in fiducial registration. Rather, it specifies a known spatial relationship. |
|||
The registration is based on fiducials that represent patient or specimen features identified in each data set in combination with global image information. |
|||
Values are derived by sampling data from a Source Image into a Registered Reference Coordinate System based on a Deformable Spatial Registration Instance. |
|||
Deformable Spatial Registration Instance used for image deformation. |
|||
A plane fiducial that specifies the location of the plane separating the two hemispheres of the brain. |
|||
A point fiducial that specifies the location in the plane perpendicular to the Anterior- Posterior-Commissure axis and tangential to the anterior limit of the right brain hemisphere. |
|||
A point fiducial that specifies the location in the plane perpendicular to the Anterior- Posterior-Commissure axis and tangential to the posterior limit of the right brain hemisphere. |
|||
A point fiducial that specifies the location in the plane perpendicular to the Anterior- Posterior-Commissure axis and tangential to the superior limit of the right brain hemisphere. |
|||
A point fiducial that specifies the location in the plane perpendicular to the Anterior- Posterior-Commissure axis and tangential to the inferior limit of the Right brain hemisphere. |
|||
A point fiducial that specifies the location in the plane perpendicular to the Anterior- Posterior-Commissure axis and tangential to the anterior limit of the left brain hemisphere. |
|||
A point fiducial that specifies the location in the plane perpendicular to the Anterior- Posterior-Commissure axis and tangential to the posterior limit of the left brain hemisphere. |
|||
A point fiducial that specifies the location in the plane perpendicular to the Anterior- Posterior-Commissure axis and tangential to the superior limit of the left brain hemisphere. |
|||
A point fiducial that specifies the location in the plane perpendicular to the Anterior- Posterior-Commissure axis and tangential to the inferior limit of the left brain hemisphere. |
|||
E.g., background of an image (that which might be encoded with Pixel Padding Value, or a Segmentation Property Type. |
|||
A segment for use as an input to an image registration process. E.g., to specify the bounding region for determining a Frame of Reference Transformation Matrix. |
|||
Root Document Title for ultrasound vascular evidence reports (worksheets). |
Retired. Replaced by (39445-2, LN, "US Doppler Vessels Report". |
||
The particular vessel branch, such as the inferior, medial or lateral. |
|||
A modifier to a 2D distance measurement to describe its orientation. E.g., a vascular distance measurement for a vessel plague could have a modifier Transverse or Longitudinal. |
|||
The angle formed between the Doppler beam line and the direction of blood flow within a region of interest in the body defined by the sample volume. |
|||
The depth of the center of the Doppler sample volume measured from skin line along the Doppler line. |
|||
Adult Congenital Cardiac Ultrasound Report (document title). |
|||
Document title of adult echocardiography procedure (evidence) report. |
|||
An image that is a pictorial representation of findings. The concept is typically used as a purpose of reference to an image, such as a depiction of myocardium segments depicting wall motion function. |
|||
The average of all scored (non-zero) Left Ventricle segment wall motion scores. |
|||
A type of clinical acquisition protocol for creating images or image-derived measurements. Acquisition protocols may be specific to a manufacturer's product. |
|||
Method for calculating left ventricular volume from two orthogonal views containing the true long axis (usually the apical 4 and 2 chamber views). Volume = [pL1 / 6] * [(4A1) ¸ (pL1) ] * [(4A2) ¸ (pL2) ]. |
|||
Method for calculating left ventricular volume from a view containing the true long axis (usually the apical 4-chamber view). Volume = [8(A)2]¸[3pL]. |
|||
Method (formula) for calculating left ventricle volumes and function derivatives (EF, SV, SI, etc.) that estimates the volume as the cube of diameter. |
|||
Method of calculating volume based on the summation of disk volumes. The disk axis is parallel to the left ventricular long axis and using a disk diameter averaged from the two chamber and four chamber views. |
|||
Method of calculating volume based on the summation of disk volumes. The disk axis is parallel to the left ventricular long axis with disk diameter taken from the four-chamber view. |
|||
Method (formula) for calculating left ventricle volumes and function derivatives (EF, SV, SI, etc.) Volume = [7.0/(2.4+D) ]*D3. |
|||
Mitral valve area (cm2) by Pressure Half-time = 220 (cm2.ms) / PHT (ms). |
|||
Hagen-Ansert, Sandra L., Textbook of Diagnostic Ultrasound, ed. 3, The C.V.Mosby Co., 1989, p. 73. . |
|||
For conduits in series ("in continuity"), volume flow is equal: A1*V1 = A2*V2. where V is the velocity. |
|||
For conduits in series ("in continuity"), volume flow is equal: A1*V1 = A2*V2. where V is the mean velocity. |
|||
For conduits in series ("in continuity"), volume flow is equal: A1*V1 = A2*V2. where V is the peak velocity. |
|||
For conduits in series ("in continuity"), volume flow is equal: A1*V1 = A2*V2. where V is the velocity time integral. |
|||
Utilizes aliasing velocity (by color Doppler) of flow into an orifice (often regurgitant or stenotic) to measure instantaneous flow rate, orifice area, and flow volume. The instantaneous flow rate = (2πr2vav ) * (απ) where vav is the constant velocity known as aliasing velocity at radius r, vp is the peak velocity at the orifice, and α is the angle in radians of the constant velocity surface. Estimated Orifice area = Flow rate / vp , where vp is the peak velocity at the orifice and the flow rate is the PISA peak flow rate. The volume flow is then the product of the orifice area and Velocity Time Integral. |
|||
Direct measurement of an area by tracing an irregular perimeter. |
|||
Mass = 1.04 * [(ST+LVID+PWT)3 - LVID3] * 0.8+ 0.6. Mass unit is grams and length in cm. |
|||
Mass = 1.05P ((b + t)2 X (2/3 (a + t) + d - d3 /3(a + t)2) - b2 (2/3a + d - d3 /3a2)) a = Semi-major axis from widest minor axis radius to apex. b = Short axis radius calculated from short axis cavity area t = Myocardial thickness calculated from short axis epicardial and cavity areas d = Truncated semi-major axis from widest short axis diameter to plane of mitral annulus. Mass unit is grams and length in cm. Schiller NB et al: Recommendations for quantification of the left ventricle by two-dimensional echocardiography, American Society of Echocardiography 2:364, 1989. . |
|||
A four point, echocardiographic numeric scoring scheme of myocardium segments based on evaluation of wall motion and ventricle morphology. Recommendations for Quantitation of the Left Ventricle by Two-Dimensional Echocardiography, Journal of the American Society of Echocardiography, 2:358-367, 1989. |
|||
A five point, echocardiographic numeric scoring scheme of myocardium segments based on evaluation of wall motion and ventricle morphology. Recommendations for Quantitation of the Left Ventricle by Two-Dimensional Echocardiography, Journal of the American Society of Echocardiography, 2:358-367, 1989. |
|||
A five point, echocardiographic numeric scoring scheme of myocardium segments based on evaluation of wall motion and ventricle morphology, with severity of hypokinesis graded. Recommendations for Quantitation of the Left Ventricle by Two-Dimensional Echocardiography, Journal of the American Society of Echocardiography, 2:358-367, 1989. |
|||
Method of estimating volume from a planar ellipse. Equivalent to Biplane Ellipse with an assumption that the ellipse in the orthogonal plane has identical major and minor diameters. |
|||
Modified Simpson's Method of estimating ventricular volume, based on the method of disks with paired apical views. Schiller NB, et al. "Recommendations for quantitation of the left ventricle by two-dimensional echocardiography. American Society of Echocardiography Committee on Standards, Subcommittee on Quantitation of Two-Dimensional Echocardiograms". J Am Soc Echocardiogr.1989 2(5):358-367. Sep-Oct. |
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Bullet method of estimating ventricular volume. |
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Color coded ultrasound images of blood flow, which depict the amplitude, or power, of Doppler signals. |
Replaced by (425704008, SCT, "Power Doppler") |
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Replaced by (426865009, SCT, "3D mode") |
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Destruction of ultrasonic contrast microbubbles by a high-energy ultrasound pulse. |
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Ultrasound transducer scan pattern in which information is gathered along a line. |
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Ultrasound transducer scan pattern in which information is gathered within a plane. |
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Ultrasound transducer scan pattern in which information is gathered within a volume. |
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Ultrasound transducer geometry characterized by a single scan line used for PW or CW Doppler scanning. |
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Ultrasonic transducer geometry characterized by parallel lines. |
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Ultrasonic transducer geometry characterized by radial lines normal to the outside of a curved surface. |
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Ultrasonic transducer geometry characterized by lines originating from a common apex. |
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Ultrasonic transducer geometry characterized by lines emanating radially from a single point. |
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Ultrasonic transducer geometry characterized by a circular ring of transducer elements. |
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Ultrasonic steering technique consisting of a single beam normal to the transducer face steered by the orientation of the probe. |
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Ultrasonic steering technique consisting of mechanically directing the beam. |
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Ultrasonic steering technique consisting of electronically-steered beams. |
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Transducer is designed to be placed onto the surface of the subject. |
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Transducer is designed for insertion into the subject via a catheter. |
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Transducer is designed for insertion into either the vaginal cavity or the rectal cavity. |
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Transducer is designed for insertion into the subject via an incision. |
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method to measure the mass of the Left Ventricle via the ASE area-length method at end diastole. LV Mass = 1.05*(5/6*(A1*(L+t)) - 5/6*(A2*L)) A1 = Left Ventricle epicardial SAX area at the level of the papillary muscle tips at end diastole. A2 = Left Ventricle endocardial SAX area cavity area at the level of the papillary muscle tips at end diastole. L = Left Ventricle apical view long axis length at end diastole. t = Myocardial thickness can be computed as: t = sqrt (A1/3.14) - sqrt (A2/3.14) 1) Schiller, N.B., et al. "Recommendations for Quantification of the LV by Two-dimensional Echocardiography." J Am Soc Echo, Vol. 2, No. 5: 358-367, Sep-Oct 1989. 2) Reichek, N., et al. "Anatomic Validation of Left Ventricular Mass Estimates from Clinical Two-dimensional Echocardiography: Initial Results." Circulation, Vol. 67, No. 2: 348-52, February 1983. |
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Equation = Left Ventricle Mass by M-mode (in gram) / (Height (in meter)) ^2.7 Giovanni De Simone, et al. "Effect of Growth on Variability of Left Ventricular Mass: Assessment of Allometric Signals in Adults and Children and Their Capacity to Predict Cardiovascular Risk". New York, New York and Cincinnati, Ohio. |
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Left Ventricle Mass by Truncated Ellipse - adjusted by Height |
Equation = Left Ventricle Mass by Truncated Ellipse / Height^2.7 Giovanni De Simone, et al. "Effect of Growth on Variability of Left Ventricular Mass: Assessment of Allometric Signals in Adults and Children and Their Capacity to Predict Cardiovascular Risk". New York, New York and Cincinnati, Ohio. |
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Equation = Left Ventricle Mass by Area Length / Height^2.7 Giovanni De Simone, et al. "Effect of Growth on Variability of Left Ventricular Mass: Assessment of Allometric Signals in Adults and Children and Their Capacity to Predict Cardiovascular Risk". New York, New York and Cincinnati, Ohio. |
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Measurements that are described by a single pre-coordinated code. |
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Measurements that are described by a collection of (generally atomic) post-coordinated codes. |
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Measurements taken in an ad hoc fashion without any coordinated semantics. |
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The source system of the measurement does not maintain a persistent pre-coordinated code by which different instances of the measurement can be associated and tracked over multiple procedures. |
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The type of observation made at the finding site, e.g., whether it is an observation of the structure of the finding site, an observation of the behavior of the finding site, or an observation of the blood flow at the finding site. |
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The type of derivation used to obtain the measurement value. E.g. whether it is taken directly, formed as a ratio, normalized against an index, or calculated using a more elaborate equation. |
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The measurement which is the denominator of a measurement that is divided. This applies to measurements such as ratios or indexed values. |
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A brief label, suitable for display on a screen or report. (Not suitable for matching). |
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Measurements that need to be associated with a specific stage in a procedure or acquisition protocol. |
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The subject of a measurement is the physical structure of the Finding Site, such as the mass or diameter. |
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The subject of a measurement is the behavior of the Finding Site, such as the velocity or duration of motion. |
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The measurement has been normalized by dividing it by an index value (such as Body Surface Area). |
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The measurement is a change value expressed as a fraction of its baseline value. E.g. cardiac ejection fraction or fractional shortening. |
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The measurement is calculated by incorporating one or more measured values into an equation other than a ratio, fractional change or indexed calculation. |
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The distal portion (at the Pulmonic Valve) of the Right Ventricle Outflow Tract. |
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The proximal portion (subvalvular) of the Right Ventricle Outflow Tract. |
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The period of time between the onset of muscle activation and the onset of force or motion. |
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The period between onset of ventricular contraction and the beginning of antegrade blood flow out of the ventricle. |
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The period of retrograde flow into the pulmonary vein during atrial contraction. |
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The period of the entire cardiac cycle. E.g. from End Systole of one heartbeat to End Systole of the next heartbeat. |
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The standard deviation over 12 left ventricle myocardial segments of the time to peak myocardial sustained systolic velocity of each segment. |
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The effective area of an orifice (such as the mitral valve orifice) during bloodflow through the orifice. |
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The distance traversed by some tissue over a defined period. |
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The maximum area of an orifice opening over a defined period. |
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The peak pressure of blood over a defined period at a defined location. |
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The radius of the proximal isovelocity surface area (PISA) of fluid flow approaching an orifice. It is commonly used to evaluate cardiac valve regurgitation. |
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A cross-sectional area of a regurgitation jet, taken perpendicular to the primary flow. |
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A width of a regurgitation jet taken perpendicular to the primary flow. |
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CARDIOsphere™ ultrasonic contrast agent produced by POINT Biomedical. |
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Echovist® ultrasonic contrast agent produced by Schering AG. |
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Imagify™ ultrasonic contrast agent produced by Accusphere Inc. |
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Levovist® ultrasonic contrast agent produced by Schering AG. |
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Sonazoid™ ultrasonic contrast agent produced by Daiichi Pharmaceutical / General Electric. |
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SonoVue™ ultrasonic contrast agent produced by Bracco Diagnostics. |
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Targestar™-B ultrasonic contrast agent produced by Targeson LLC. |
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Targestar™-P ultrasonic contrast agent produced by Targeson LLC. |
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A structured report containing the quantitative results of human or machine analysis of images. |
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A structured report containing the quantitative results of human or machine analysis of images for oncology evaluation. |
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A structured report containing the quantitative results of human or machine analysis of DCE-MR. |
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A structured report containing the quantitative results of human or machine analysis of PET images. |
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An MRI procedure in which multiple parameters including diffusion, dynamic contrast and T2 are measured. |
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An MRI procedure of the prostate in which multiple parameters including diffusion, dynamic contrast and T2 are measured. |
Replaced by (719178004, SCT, "Multiparametric MRI of prostate") |
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An MRI procedure of the whole body in which multiple parameters including diffusion, dynamic contrast and T2 are measured. |
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Method of calculation of the volume of an ellipsoid as length * width * height * π / 6. |
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Method of summing the volumes of all the voxels (and partial voxels if the segment contains partially occupied voxels) included in the segment to derive a total volume. |
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Maximum average gray value that is calculated from a 1 cubic centimeter sphere placed within the region of interest. See Wahl RL, Jacene H, Kasamon Y, Lodge MA. From RECIST to PERCIST: Evolving Considerations for PET Response Criteria in Solid Tumors. Journal of Nuclear Medicine. 2009;50(Suppl 1):122S - 150S. |
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The volume of a lesion (e.g., a tumor) ascertained through information about its metabolic activity (e.g., SUV on PET). Abbreviated "MV". Synonymous with Metabolic Tumor Volume (MTV). |
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The total activity of a lesion obtained as the product of its volume and its glycolytic activity (on FDG-PET). The volume may be defined on the same modality (e.g., the MV on FDG-PET by some thresholding or other technique) or on another spatially registered modality (e.g., the lesion outline segmented on CT or MR). Does not apply to other radiopharmaceuticals than those involved in glucose metabolism. Abbreviated TLG. Synonymnous with "Tumor Lesion Glycolysis". |
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The amount glycolytic activity summed across all voxels in a defined region or within a defined range of SUV (on FDG-PET). |
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The total activity of a lesion obtained as the product of its volume and its proliferative activity (on FLT-PET). The volume may be defined on the same modality (e.g., the MV on FDG-PET by some thresholding or other technique) or on another spatially registered modality (e.g., the lesion outline segmented on CT or MR). Does not apply to other radiopharmaceuticals than those involved in cellular proliferation. Abbreviated TLP. Synonymnous with "Tumor Lesion Proliferation". |
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The amount proliferative activity summed across all voxels in a defined region or within a defined range of SUV (on FLT-PET). |
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A background-corrected, partial volume independent version of TLG. SAM is calculated by drawing a volume of interest (VOI1) around the tumour and a larger VOI (VOI2) around VOI1. Subtracting the background activity in VOI2-VOI1 from VOI1 yields SAM. See Mertens et al. "Standardized added metabolic activity (SAM): a partial volume independent marker of total lesion glycolysis in liver metastases". Eur J Nucl Med Mol Imaging (2012) 39:1441-1448. |
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The background value (VOI2-VOI1) used to calculate Standardized Added Metabolic Activity (SAM). SAM is calculated by drawing a volume of interest (VOI1) around the tumour and a larger VOI (VOI2) around VOI1. Subtracting the background activity in VOI2-VOI1 from VOI1 yields SAM. See Mertens et al. "Standardized added metabolic activity (SAM): a partial volume independent marker of total lesion glycolysis in liver metastases". Eur J Nucl Med Mol Imaging (2012) 39:1441-1448. |
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The ratio of the SUV within a tumor to the SUV of a pre-defined background region. A more general concept than Tumor to Background Ratio (TBR). |
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The SUV of a pre-defined background region used to compute Lesion to Background SUV Ratio. |
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A statistical index of complexity comparing how detail in a fractal pattern changes with the scale at which it is measured; a ratio of the change in detail to the change in scale. |
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Measure of the asymmetry of the probability distribution of a real-valued random variable about its mean. |
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Measure of the peakedness of the probability distribution of a real-valued random variable. |
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The zero order entropy of a Gray Level Co-occurrence Matrix (GLCM). A measure of disorder. Abbreviated ENT. See Fcm.joint.entr in [IBSI Features]. |
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The square root of the Angular Second Moment (ASM) of a Gray Level Co-occurrence Matrix (GLCM). A measure of orderliness. |
Sometimes referred to as "energy", "uniformity" or "uniformity of energy" but then potentially confused with ASM. Not defined in [IBSI Features] |
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The Inverse Difference Moment (homogeneity) of a Gray Level Co-occurrence Matrix (GLCM). Abbreviated IDM. See Fcm.inv.diff.mom in [IBSI Features]. |
Other concepts are sometimes referred to as "homogeneity", e.g., the "inverse difference", which is calculated from the absolute value of differences rather than square of them. Replaced by (WF0Z, IBSI, "Inverse Difference Moment of GLCM"). |
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The sum of squares of a Gray Level Co-occurrence Matrix (GLCM). A measure of gray level variations. Abbreviated CON. See Fcm.contrast in [IBSI Features]. |
Distinct from "joint (sum of squares) variance" and "dissimilarity". |
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The dissimilarity of a Gray Level Co-occurrence Matrix (GLCM). Abbreviated DIS. See Fcm.dissimilarity in [IBSI Features]. |
Distinct from "contrast", which uses square rather than absolute value of difference. |
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The Angular Second Moment of a Gray Level Co-occurrence Matrix (GLCM). Abbreviated ASM. See Fcm.energy in [IBSI Features]. |
Sometimes referred to as "energy", "uniformity" or "uniformity of energy" but then potentially confused with square root of ASM. |
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A measure of the linear dependency of gray levels on those of neighbouring pixels of a Gray Level Co-occurrence Matrix (GLCM). Abbreviated COR. See Fcm.corr in [IBSI Features]. |
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A tabulation of how often different combinations of pixel values (gray levels) occur in an image. Abbreviated GLCM. See [IBSI Features]. |
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An identifier of a specific time point in a continuum, which is unique within an appropriate local context (such as an entire organization, system or treatment protocol), which identifies the time point for a specific patient. |
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An identifier of a specific time point in a continuum, which is unique within an appropriate local context (such as an entire organization, system or treatment protocol), which identifies the time point "slot" within a treatment protocol using the same value for all patients in the protocol. |
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A number indicating the order of a time point relative to other time points in the same continuum. |
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Similar but not identical to (21954-3, LN, "Protocol eligibility status Cancer"), since not constrained to cancer, etc. |
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Response Evaluation Criteria in Solid Tumors version 1.0. See [RECIST] in Normative References. |
More specific than (112022, DCM, "RECIST") or (C1709926, UMLS, "RECIST") or (C49164, NCIt, "RECIST") in that a specific version is specified. |
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Response Evaluation Criteria in Solid Tumors Version 1.1. See Eisenhauer et al. "New Response Evaluation Criteria in Solid Tumours: Revised RECIST Guideline (version 1.1)." European Journal of Cancer 45, no. 2 (n.d.): 228-47. doi:10.1016/j.ejca.2008.10.026. |
More specific than (112022, DCM, "RECIST") or (C1709926, UMLS, "RECIST") or (C49164, NCIt, "RECIST") in that a specific version is specified. |
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A reference to the Real World Value Map applied to the stored image pixel values before their use for a measurement |
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A container that groups common information about a set of images used as evidence to produce a report. |
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The time between the start of injection of the PET radionuclide and the start of acquisition of the PET data. |
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Coefficient of determination, R2. An indication of goodness of fit. |
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Durbin-Watson statistic for detecting serial correlation in residuals. See http://en.wikipedia.org/wiki/Durbin%E2%80%93Watson_statistic. |
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Akaike information criterion. A measure of the balance between goodness of fit and number of free parameters. See Akaike H. A new look at the statistical model identification. IEEE Transactions on Automatic Control. 1974 Dec;19(6):716-23. http://dx.doi.org/10.1109/TAC.1974.1100705. |
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Bayesian information criterion. A measure of the balance between goodness of fit and model complexity. See http://en.wikipedia.org/wiki/Bayesian_information_criterion. |
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Perfusion analysis by Arterial Spin Labeling (ASL) MR technique |
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Ktrans, the volume transfer constant of a tracer diffusion kinetic model, specifically the volume transfer constant between blood plasma and extravascular extracellular space (EES) See Tofts et al, "Estimating Kinetic Parameters From Dynamic Contrast-Enhanced T1-Weighted MRI of a Diffusable Tracer: Standardized Quantities and Symbols", Journal of Magnetic Resonance Imaging, vol. 10, pp. 223-232, 1999. |
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kep, the rate constant between extravascular extracellular space (EES) and blood plasma See Tofts et al, "Estimating Kinetic Parameters From Dynamic Contrast-Enhanced T1-Weighted MRI of a Diffusable Tracer: Standardized Quantities and Symbols", Journal of Magnetic Resonance Imaging, vol. 10, pp. 223-232, 1999. |
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ve, the fractional (not absolute) volume of extravascular extracellular space (EES) per unit volume of tissue See Tofts et al, "Estimating Kinetic Parameters From Dynamic Contrast-Enhanced T1-Weighted MRI of a Diffusable Tracer: Standardized Quantities and Symbols", Journal of Magnetic Resonance Imaging, vol. 10, pp. 223-232, 1999. |
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The initial area under the contrast agent concentration-time curve |
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The initial area under the contrast agent concentration-time curve at 60 seconds after the onset time |
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The initial area under the contrast agent concentration-time curve at 90 seconds after the onset time |
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The initial area under the contrast agent concentration-time curve at 180 seconds after the onset time |
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The initial area under the contrast agent concentration-time curve, normalized with the corresponding arterial input function, such that IAUCBN = IAUC / IAUCAIF. |
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The initial area under the contrast agent concentration-time curve at 60 seconds after the onset time, normalized with the corresponding arterial input function, such that IAUC60BN = IAUC60 / IAUC60AIF. |
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The initial area under the contrast agent concentration-time curve at 90 seconds after the onset time, normalized with the corresponding arterial input function, such that IAUC90BN = IAUC90 / IAUC90AIF. |
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The initial area under the contrast agent concentration-time curve at 180 seconds after the onset time, normalized with the corresponding arterial input function, such that IAUC180BN = IAUC180 / IAUC180AIF. |
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τm. The mean intracellular water lifetime (τi). Used in the Shutter-Speed Model (SSM) of tracer kinetics. |
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vp. The fractional (not absolute) blood plasma volume per unit volume of tissue. See Tofts et al, "Estimating Kinetic Parameters From Dynamic Contrast-Enhanced T1-Weighted MRI of a Diffusable Tracer: Standardized Quantities and Symbols", Journal of Magnetic Resonance Imaging, vol. 10, pp. 223-232, 1999. |
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A tracer diffusion kinetic model in which the permeability is assumed to be isodirectional. See P. Tofts, "Modeling tracer kinetics in dynamic Gd-DTPA MR imaging", Journal of Magnetic Resonance Imaging, vol. 7, pp. 91-101, 1997. Mathematically equivalent to the model proposed by Kety in a non-MRI context, hence sometimes refered to as the Tofts-Kety (TK) model. See Kety SS. The Theory and Applications of the Exchange of Inert Gas at the Lungs and Tissues. Pharmacological Reviews. 1951 Mar 1;3(1):1-41. |
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A tracer diffusion kinetic model in which the permeability is not assumed to be isodirectional, and which includes the contribution of tracer in the blood plasma to the total tissue concentration. See P. Tofts, "Modeling tracer kinetics in dynamic Gd-DTPA MR imaging", Journal of Magnetic Resonance Imaging, vol. 7, pp. 91-101, 1997. |
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A semiquantitative analysis of the contrast-enhancement concentration versus time curve that avoids the use of a pharmacokinetic model. E.g., integration to compute the initial area under the curve. |
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A tracer diffusion kinetic model that accounts for the tumor leakage profile during the first pass of contrast. See Li, Ka-Loh, Xiao Ping Zhu, John Waterton, and Alan Jackson. "Improved 3D Quantitative Mapping of Blood Volume and Endothelial Permeability in Brain Tumors." Journal of Magnetic Resonance Imaging 12, no. 2 (2000): 347-357. doi:10.1002/1522-2586(200008)12:2<347::AID-JMRI19>3.0.CO;2-7. |
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A tracer diffusion kinetic model that does not assume that intercompartmental water molecule exchange is infinitely fast. See Li, Xin, Wei Huang, Thomas E. Yankeelov, Alina Tudorica, William D. Rooney, and Charles S. Springer. "Shutter-Speed Analysis of Contrast Reagent Bolus-Tracking Data: Preliminary Observations in Benign and Malignant Breast Disease." Magnetic Resonance in Medicine 53, no. 3 (2005): 724-29. doi:10.1002/mrm.20405. |
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A tracer diffusion kinetic model that mathematically unifies the Tofts, Extended Tofts, Adiabatic Tissue Homogeneity, and Two Compartment Exchange models See Schabel MC. A unified impulse response model for DCE-MRI. Magnetic Resonance in Medicine. 2012;68(5):1632-46. doi:10.1002/mrm.24162. |
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An adiabatic approximation to the tissue homogeneity tracer diffusion kinetic model, which assumes that the tracer concentration in parenchymal tissue changes slowly relative to that in capillaries. See St. Lawrence KS, Lee T-Y. An Adiabatic Approximation to the Tissue Homogeneity Model for Water Exchange in the Brain: I. Theoretical Derivation. J Cereb Blood Flow Metab. 1998 Dec;18(12):1365-77. doi:10.1097/00004647-199812000-00011. |
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A tracer diffusion kinetic that incorporates the extracellular space of the lesion as a peripheral compartment, connected to the central (plasma) compartment by linear exchange processes in both directions. See Brix G, Semmler W, Port R, Schad LR, Layer G, Lorenz WJ. Pharmacokinetic Parameters in CNS Gd-DTPA Enhanced MR Imaging. Journal of Computer Assisted Tomography. 1991;15(4):621-8. |
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T1 measurement by Multiple Flip Angles (MFA) (variable saturation) method |
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Calculation was performed using a fixed value of T1 rather than a measured value. The value could be encoded as the value of (126353, DCM, "T1 Used For Calculation"). |
|||
An Arterial Input Function computed from a user-defined Region of Interest. |
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An Arterial Input Function computed from an automatically detected Region of Interest. |
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A data-driven blind source separation (BSS) algorithm that estimates AIF from individuals without any presumed AIF model and initialization. See Lin, Yu-Chun, Tsung-Han Chan, Chong-Yung Chi, Shu-Hang Ng, Hao-Li Liu, Kuo-Chen Wei, Yau-Yau Wai, Chun-Chieh Wang, and Jiun-Jie Wang. "Blind Estimation of the Arterial Input Function in Dynamic Contrast-Enhanced MRI Using Purity Maximization." Magnetic Resonance in Medicine 68, no. 5 (November 1, 2012): 1439-49. doi:10.1002/mrm.24144. |
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The time at which the concentration-time curve achieves its peak for the first time. Used as a concept name for a value or as a method. E.g., used as a method of calculation for BAT. See Shpilfoygel Med Phys 2008. doi:10.1118/1.1288669. |
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The nominal time at which arrival of a contrast bolus is detected, which is used as a reference point for subsequent calculations. Used as a concept name for a value or as a method. No specific computational method is implied by this general definition. Abbreviated BAT. |
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The time at which the concentration-time curve achieves half of its peak density for the first time. Used as a concept name for a value or as a method. E.g., used as a method of calculation for BAT. See Shpilfoygel Med Phys 2008. doi:10.1118/1.1288669. |
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A method of determining BAT that involves computing the temporal derivative of the concentration-time curve and selecting the time when the temporal derivative exceeds a specified threshold. See Shpilfoygel Med Phys 2008. doi:10.1118/1.1288669. |
|||
A threshold applied to the temporal derivative of the concentration-time curve. E.g., used to establish BAT. See Shpilfoygel Med Phys 2008. doi:10.1118/1.1288669. |
|||
The maximum rate of signal intensity change within a measured region of a time-activity curve. See Boonsirikamchai, Piyaporn, Harmeet Kaur, Deborah A. Kuban, Edward Jackson, Ping Hou, and Haesun Choi. "Use of Maximum Slope Images Generated From Dynamic Contrast-Enhanced MRI to Detect Locally Recurrent Prostate Carcinoma After Prostatectomy: A Practical Approach." American Journal of Roentgenology 198, no. 3 (March 1, 2012): W228-W236. doi:10.2214/AJR.10.6387. |
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The maximum degree of signal intensity change within a measured region of a time-activity curve. See Boonsirikamchai, Piyaporn, Harmeet Kaur, Deborah A. Kuban, Edward Jackson, Ping Hou, and Haesun Choi. "Use of Maximum Slope Images Generated From Dynamic Contrast-Enhanced MRI to Detect Locally Recurrent Prostate Carcinoma After Prostatectomy: A Practical Approach." American Journal of Roentgenology 198, no. 3 (March 1, 2012): W228-W236. doi:10.2214/AJR.10.6387. |
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Tracer concentration in tissue. E.g., in a DCE-MR experiment, the concentration of contrast agent in mmol/l. |
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The degree to which a paramagnetic contrast agent can enhance the proton longitudinal relaxation rate constant (R1, 1/T1), normalized to the concentration of the contrast agent. Also referred to as r1. Typically expressed in units of l/mmol/s. |
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The absolute flow rate of blood perfusing a region as volume per mass per unit of time. The mass divisor may be approximated by a measurement of volume assuming a tissue density of 1. |
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The absolute volume of blood perfusing a region as volume per mass. The mass divisor may be approximated by a measurement of volume assuming a tissue density of 1. |
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The percent of the oxygen removed from the blood by tissue during its passage through the capillary network. For example, as measured by blood oxygenation level dependent (BOLD) MR. See He, Xiang, and Dmitriy A. Yablonskiy. "Quantitative BOLD: Mapping of Human Cerebral Deoxygenated Blood Volume and Oxygen Extraction Fraction: Default State." Magnetic Resonance in Medicine 57, no. 1 (2007): 115-26. |
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The longitiudinal relaxation rate constant for the decay of longitiudinal magnetization caused by spin-lattice relaxation. The inverse of longitudinal relaxation time, i.e., R1 = 1/T1. |
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The transverse relaxation rate constant for the decay of transverse magnetization caused by spin-spin relaxation. The inverse of transverse relaxation time, i.e., R2 = 1/T2. |
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The transverse relaxation rate constant for the decay of transverse magnetization caused by a combination of spin-spin relaxation and magnetic field inhomogeneity. The inverse of transverse relaxation time, i.e., R2* = 1/T2*. |
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Magnetic Susceptibility is a measure of the amount of magnetization induced in a material when placed in an external magnetic field. It is the quantity encoded as the voxel intensity in Quantitative Susceptibility Map (QSM) images. It is a dimensionless quantity, usually recorded with units of parts per millions (ppm). See Liu T, Wisnieff C, Lou M, Chen W, Spincemaille P, Wang Y. Nonlinear formulation of the magnetic field to source relationship for robust quantitative susceptibility mapping. Magnetic Resonance in Medicine. 2013;69(2):467-76. http://dx.doi.org/10.1002/mrm.24272. See Wang Y, Liu T. Quantitative susceptibility mapping (QSM): Decoding MRI data for a tissue magnetic biomarker. Magnetic Resonance in Medicine. 2015;73(1):82-101. http://dx.doi.org/10.1002/mrm.25358. |
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The relative flow rate of blood perfusing a region. Obtained by dividing the absolute flow rate of blood perfusing a region by the absolute flow rate of blood perfusing a reference region. |
|||
The relative volume of blood perfusing a region. Obtained by dividing the absolute volume of blood perfusing a region by the absolute volume of blood perfusing a reference region. |
|||
A ratio of locally measured radioactivity concentration versus the injected radioactivity distributed evenly throughout the whole body. This general concept encompasses all specific methods of calculating the whole body volume of distribution, such as using body weight, lean body mass, body surface area, etc. |
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Standardized Uptake Value calculated using body weight. The patient size correction factor for males and females is body weight. Defined in Sugawara et al. Reevaluation of the Standardized Uptake Value for FDG: Variations with Body Weight and Methods for Correction.Radiology, 1999 at http://radiology.rsna.org/content/213/2/521 |
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Standardized Uptake Value calculated using lean body mass by James method. The patient size correction factor for males is 1.10 * weight - (120 or 128) * (weight/height) ^2, and for females is 1.07 * weight - 148 * (weight/height) ^2. Defined in Sugawara et al. Reevaluation of the Standardized Uptake Value for FDG: Variations with Body Weight and Methods for Correction.Radiology, 1999 at http://radiology.rsna.org/content/213/2/521, except that either 120 or 128 may be used as the multiplier parameter for males). Unfortunately, Sugawara used a parameter of 120 rather than 128, propagating an error in Morgan DJ, Bray KM. Lean Body Mass as a Predictor of Drug Dosage: Implications for Drug Therapy. Clinical Pharmacokinetics. 1994;26(4):292-307, which misquoted the original LBM definition that used 128 in James WPT, Waterlow JC. Research on Obesity: A Report of the DHSS/MRC Group. London: Her Majesty’s Stationery Office; 1976. Implementations differ in whether they have used 120 or 128 when using this code. See Kelly M. SUV: Advancing Comparability and Accuracy. Siemens; 2009. Available from: http://www.mpcphysics.com/documents/SUV_Whitepaper_Final_11.17.09_59807428_2.pdf. |
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Standardized Uptake Value calculated using body surface area. The patient size correction factor for males and females is weight^ 0.425 * height^0.725 * 0.007184. Defined in Sugawara et al. Reevaluation of the Standardized Uptake Value for FDG: Variations with Body Weight and Methods for Correction.Radiology, 1999 at http://radiology.rsna.org/content/213/2/521 |
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Standardized Uptake Value calculated using ideal body weight. The patient size correction factor for males is 48.0 + 1.06 * (height - 152) and for females is 45.5 + 0.91 * (height - 152). Defined in Sugawara et al. Reevaluation of the Standardized Uptake Value for FDG: Variations with Body Weight and Methods for Correction.Radiology, 1999 at http://radiology.rsna.org/content/213/2/521 |
|||
Standardized Uptake Value calculated using lean body mass by Janmahasatian method. The patient size correction factor for males is 9.27E3 * weight / (6.68E3 + 216 * weight / (height^2)) and for females is 9.27E3 * weight / (8.78E3 + 244 * weight / (height^2)). Defined in Janmahasatian et al. Quantification of Lean Bodyweight. Clin Pharmacokinet. 2005 Oct 1;44(10):1051-65. at http://dx.doi.org/10.2165/00003088-200544100-00004 and its role in SUVlbm(Janma) calculation is discussed in Tahari et al. Optimum Lean Body Formulation for Correction of Standardized Uptake Value in PET Imaging. Journal of Nuclear Medicine. 2014 Sep 1;55(9):1481-4. at http://jnm.snmjournals.org/content/55/9/1481. |
|||
Standardized Uptake Value calculated using lean body mass by James method, using the originally published 128 multiplier for males. The patient size correction factor for males is 1.10 * weight - 128) * (weight/height) ^2, and for females is 1.07 * weight - 148 * (weight/height) ^2. |
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Method of calculating Standardized Uptake Value using body weight. The patient size correction factor for males and females is body weight. Defined in Sugawara et al. Reevaluation of the Standardized Uptake Value for FDG: Variations with Body Weight and Methods for Correction.Radiology, 1999 at http://radiology.rsna.org/content/213/2/521 |
|||
Method of calculating Standardized Uptake Value using lean body mass. The patient size correction factor for males is 1.10 * weight - (120 or 128) * (weight/height) ^2, and for females is 1.07 * weight - 148 * (weight/height) ^2. Defined in Sugawara et al. Reevaluation of the Standardized Uptake Value for FDG: Variations with Body Weight and Methods for Correction.Radiology, 1999 at http://radiology.rsna.org/content/213/2/521 Unfortunately, Sugawara used a parameter of 120 rather than 128, propagating an error in Morgan DJ, Bray KM. Lean Body Mass as a Predictor of Drug Dosage: Implications for Drug Therapy. Clinical Pharmacokinetics. 1994;26(4):292-307, which misquoted the original LBM definition that used 128 in James WPT, Waterlow JC. Research on Obesity: A Report of the DHSS/MRC Group. London: Her Majesty’s Stationery Office; 1976. Implementations differ in whether they have used 120 or 128 when using this code. See Kelly M. SUV: Advancing Comparability and Accuracy. Siemens; 2009. Available from: http://www.mpcphysics.com/documents/SUV_Whitepaper_Final_11.17.09_59807428_2.pdf. |
|||
Method of calculating Standardized Uptake Value using body surface area. The patient size correction factor for males and females is weight^ 0.425 * height^0.725 * 0.007184. Defined in Sugawara et al. Reevaluation of the Standardized Uptake Value for FDG: Variations with Body Weight and Methods for Correction.Radiology, 1999 at http://radiology.rsna.org/content/213/2/521 |
|||
Method of calculating Standardized Uptake Value using ideal body weight. The patient size correction factor for males is 48.0 + 1.06 * (height - 152) and for females is 45.5 + 0.91 * (height - 152). Defined in Sugawara et al. Reevaluation of the Standardized Uptake Value for FDG: Variations with Body Weight and Methods for Correction.Radiology, 1999 at http://radiology.rsna.org/content/213/2/521 |
|||
Janmahasatian method of calculating Standardized Uptake Value using lean body mass. The patient size correction factor for males is 9.27E3 * weight / (6.68E3 + 216 * weight / (height^2)) and for females is 9.27E3 * weight / (8.78E3 + 244 * weight / (height^2)). Defined in Janmahasatian et al. Quantification of Lean Bodyweight. Clin Pharmacokinet. 2005 Oct 1;44(10):1051-65. at http://dx.doi.org/10.2165/00003088-200544100-00004 and its role in SUVlbm(Janma) calculation is discussed in Tahari et al. Optimum Lean Body Formulation for Correction of Standardized Uptake Value in PET Imaging. Journal of Nuclear Medicine. 2014 Sep 1;55(9):1481-4. at http://jnm.snmjournals.org/content/55/9/1481. |
|||
James method of calculating Standardized Uptake Value using lean body mass with the originally published 128 multiplier for males. The patient size correction factor for males is 1.10 * weight - 128) * (weight/height) ^2, and for females is 1.07 * weight - 148 * (weight/height) ^2. |
|||
A beta-amyloid PET radiotracer that is an analog of thioflavin T. |
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A radioconjugate consisting of n-acetylaspartylglutamate labeled with lutetium Lu 177 used as a radiotracer. |
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Replaced with (126503, DCM, "Flubatine F^18^"). |
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An I 124 cancer targeted phospholipid ether PET radiotracer. |
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An I 131 cancer targeted phospholipid ether PET radiotracer. |
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A PET radiotracer used for tau brain imaging. See Harada R, Okamura N, Furumoto S, Furukawa K, Ishiki A, Tomita N, et al. 18F-THK5351: A Novel PET Radiotracer for Imaging Neurofibrillary Pathology in Alzheimer Disease. Journal of Nuclear Medicine. 2016 Feb 1;57(2):208-14. doi:10.2967/jnumed.115.164848 |
Replaced with (C4279748, UMLS, "THK5351 F^18^"). |
||
A PET radiotracer used for myocardial perfusion imaging. See Yu M, Nekolla SG, Schwaiger M, Robinson SP. The Next Generation of Cardiac Positron Emission Tomography Imaging Agents: Discovery of Flurpiridaz F-18 for Detection of Coronary Disease. Seminars in Nuclear Medicine. 2011 Jul;41(4):305-13. doi:10.1053/j.semnuclmed.2011.02.004 See SNMMI. Flurpiridaz. http://interactive.snm.org/docs/PET_PROS/flurpiridaz_%2007_30_12_Final.pdf |
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A PET radiotracer used for tau brain imaging. See Wong DF, Comley R, Kuwabara H, Rosenberg PB, Resnick SM, Ostrowitzki S, et al. First in-human PET study of 3 novel tau radiopharmaceuticals: [11C]RO6924963, [11C]RO6931643, and [18F]RO6958948. J Nucl Med. 2018 May 4; doi:10.2967/jnumed.118.209916. http://jnm.snmjournals.org/content/early/2018/05/03/jnumed.118.209916 |
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A PET radiotracer used for tau brain imaging. See Wong DF, Comley R, Kuwabara H, Rosenberg PB, Resnick SM, Ostrowitzki S, et al. First in-human PET study of 3 novel tau radiopharmaceuticals: [11C]RO6924963, [11C]RO6931643, and [18F]RO6958948. J Nucl Med. 2018 May 4; doi:10.2967/jnumed.118.209916. http://jnm.snmjournals.org/content/early/2018/05/03/jnumed.118.209916 |
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A Zr 89 nanocolloidal albumin PET Radiotracer. See Heuveling et al. Pilot Study on the Feasibility of PET/CT Lymphoscintigraphy with 89Zr-Nanocolloidal Albumin for Sentinel Node Identification in Oral Cancer Patients. J Nucl Med. 2013 Apr;54(4):585-9. doi:10.2967/jnumed.112.115188. http://jnm.snmjournals.org/content/54/4/585.long |
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A PET radiotracer used for tau brain imaging. See Wong DF, Comley R, Kuwabara H, Rosenberg PB, Resnick SM, Ostrowitzki S, et al. First in-human PET study of 3 novel tau radiopharmaceuticals: [11C]RO6924963, [11C]RO6931643, and [18F]RO6958948. J Nucl Med. 2018 May 4; doi:10.2967/jnumed.118.209916. http://jnm.snmjournals.org/content/early/2018/05/03/jnumed.118.209916 |
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A PET radiotracer targeting PMSA used for prostate cancer imaging. See Giesel FL, Hadaschik B, Cardinale J, Radtke J, Vinsensia M, Lehnert W, et al. F-18 labelled PSMA-1007: biodistribution, radiation dosimetry and histopathological validation of tumor lesions in prostate cancer patients. Eur J Nucl Med Mol Imaging. 2017 Apr 1;44(4):678–88. doi:10.1007/s00259-016-3573-4. http://link.springer.com/article/10.1007/s00259-016-3573-4 |
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A PET radiotracer targeting PMSA used for prostate cancer imaging. See Afshar-Oromieh A, Hetzheim H, Kratochwil C, Benesova M, Eder M, Neels OC, et al. The Theranostic PSMA Ligand PSMA-617 in the Diagnosis of Prostate Cancer by PET/CT: Biodistribution in Humans, Radiation Dosimetry, and First Evaluation of Tumor Lesions. J Nucl Med. 2015 Nov 1;56(11):1697–705. doi: 10.2967/jnumed.115.161299. http://jnm.snmjournals.org/content/56/11/1697 |
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A Zr 89 Df-FK peptide PET Radiotracer. See Jacobsen O et al. MicroPET Imaging of Integrin αvβ3 Expressing Tumors Using 89Zr-RGD Peptides. Mol Imaging Biol. 2011 Dec; 13(6): 1224-1233. doi:10.1007/s11307-010-0458-y. http://www.ncbi.nlm.nih.gov/pmc/articles/PMC3137711/ |
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A Zr 89 Df-FK-PEG(3) peptide PET Radiotracer. See Jacobsen O et al. MicroPET Imaging of Integrin αvβ3 Expressing Tumors Using 89Zr-RGD Peptides. Mol Imaging Biol. 2011 Dec; 13(6): 1224-1233. doi:10.1007/s11307-010-0458-y. http://www.ncbi.nlm.nih.gov/pmc/articles/PMC3137711/ |
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A Zr 89 Df-[FK](2) peptide PET Radiotracer. See Jacobsen O et al. MicroPET Imaging of Integrin αvβ3 Expressing Tumors Using 89Zr-RGD Peptides. Mol Imaging Biol. 2011 Dec; 13(6): 1224-1233. doi:10.1007/s11307-010-0458-y. http://www.ncbi.nlm.nih.gov/pmc/articles/PMC3137711/ |
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A Zr 89 Df-[FK](2)-3PEG(4) peptide PET Radiotracer. See Jacobsen O et al. MicroPET Imaging of Integrin αvβ3 Expressing Tumors Using 89Zr-RGD Peptides. Mol Imaging Biol. 2011 Dec; 13(6): 1224-1233. doi:10.1007/s11307-010-0458-y. http://www.ncbi.nlm.nih.gov/pmc/articles/PMC3137711/ |
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An I125 translocator protein (TSPO) SPECT tracer. See Wang H, Pullambhatla M, Guilarte TR, Mease RC, Pomper MG. Synthesis of [125I]IodoDPA-713, a New Probe for Imaging Inflammation. Biochem Biophys Res Commun. 2009 Nov 6;389(1):80–3. doi:10.1007/10.1016/j.bbrc.2009.08.102 http://www.ncbi.nlm.nih.gov/pmc/articles/PMC2764231/ |
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A C11 translocator protein (TSPO) PET tracer. See Endres CJ, Pomper MG, James M, Uzuner O, Hammoud DA, Watkins CC, et al. Initial Evaluation of 11C-DPA-713, a Novel TSPO PET Ligand, in Humans. J Nucl Med. 2009 Aug;50(8):1276–82. doi:10.2967/jnumed.109.062265 http://www.ncbi.nlm.nih.gov/pmc/articles/PMC2883612/ |
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An F18 translocator protein (TSPO) PET tracer. See Vicidomini C, Panico M, Greco A, Gargiulo S, Coda ARD, Zannetti A, et al. In vivo imaging and characterization of [18F]DPA-714, a potential new TSPO ligand, in mouse brain and peripheral tissues using small-animal PET. Nuclear Medicine and Biology. 2015 Mar 1;42(3):309–16. doi:10.1016/j.nucmedbio.2014.11.009 |
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Patient Support isocentric rotation (in the IEC FIXED REFERENCE Coordinate System) as defined by [IEC 61217]. DICOM represents this value as a Continuous Rotation Angle in degrees. |
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Pitch of the Table Top (in the IEC TABLE TOP Coordinate System) as defined by [IEC 61217]. DICOM represents this value as a Continous Rotation Angle in degrees. |
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Roll of the Table Top (in the IEC TABLE TOP Coordinate System) as defined by [IEC 61217]. DICOM represents this value as a Continous Rotation Angle in degrees. |
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Eccentric axis offset, in mm (in the IEC PATIENT SUPPORT Coordinate System) as defined by [IEC 61217]. |
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Table Top eccentric rotation (in the IEC TABLE TOP ECCENTRIC Coordinate System) as defined by [IEC 61217]. DICOM represents this value as a Continuous Rotation Angle in degrees. |
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Lateral displacement of the table top, in mm (in the IEC TABLE TOP Coordinate System) as defined by [IEC 61217]. |
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Longitudinal displacement of the table top, in mm (in the IEC TABLE TOP Coordinate system) as defined by [IEC 61217]. |
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Vertical displacement of the table top, in mm (in the IEC TABLE TOP Coordinate System) as defined by [IEC 61217]. |
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Rotation of the gantry (around the Y-axis of the IEC FIXED REFERENCE Coordinate System) as defined by [IEC 61217]. DICOM represents this value as a Continuous Rotation Angle in degrees. |
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Pitch angle of rotation of the gantry around the X-axis of the IEC GANTRY Coordinate System. This parameter is not specifically defined by [IEC 61217], but is consistent with [IEC 61217]. DICOM represents this value as a Continuous Rotation Angle in degrees. |
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Yaw angle of rotation of the gantry around the Z-axis of the IEC GANTRY Coordinate System This parameter is not specifically defined by [IEC 61217], but is consistent with [IEC 61217]. DICOM represents this value as a Continuous Rotation Angle in degrees. |
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The body position of the imaging subject relative to the imaging equipment is with the subject's left side positioned towards the front of the equipment viewed from the front |
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The body position of the imaging subject relative to the imaging equipment is with the subject's right side positioned towards the front of the equipment viewed from the front |
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The body position of the imaging subject relative to the imaging equipment is with the subject's posterior (dorsal) side positioned towards the front of the equipment viewed from the front |
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The body position of the imaging subject relative to the imaging equipment is with the subject's anterior (ventral) side positioned towards the front of the equipment viewed from the front |
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The International Laboratory Code Registry (ILCR) of the Institute of Laboratory Animal Research (ILAR). See http://dels.nas.edu/global/ilar/lab-codes. |
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A description of the conditions present during acquisition of images of small animals during preclinical research. |
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The conditions present related to the handling of an animal during a specified phase. |
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A specified phase of handling of an animal (e.g., transport, preparation). |
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A description of biosafety conditions (e.g., present during small animal handling for research). |
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A description of heating conditions (e.g., present during small animal handling for research). |
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A description of Circadian effects (e.g., present during small animal handling for research). |
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A form of face mask that fits over the nose used for delivery of inhalational anesthesia (usually for small animals) |
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Cannula inserted in the nose used for delivery of inhalational anesthesia or other inhaled gases. |
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A route of administration of a substance via the retro-orbital venous sinus. Yardeni T et al. (2011). Retro-orbital injections in mice. Lab Animal, 40(5), 155-160. doi:10.1038/laban0511-155. http://www.ncbi.nlm.nih.gov/pmc/articles/PMC3158461/ |
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The phase of handling of an animal that provides their normal environment between procedures. |
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The phase of handling of an animal that is transport between environments. |
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The phase of handling of an animal that is staging prior to an imaging procedure (e.g., after removal from their home environment and transport cage, and awaiting preparation, induction or imaging). During this phase the animals are not subject to intervention (e.g., injection, catheterization) (cf. 127104, DCM, "Preparation for imaging")). |
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The phase of handling of an animal that is preparation prior to an imaging procedure that involves handling and intervention (e.g., such as injection, catheterization) (cf. 127103, DCM, "Staging prior to imaging")). |
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The phase of handling of an animal during which the housing conditions are applicable. |
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The identifier of the room in which racks of animal cages are housed. |
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The manufacturer's product name of the animal housing unit (or bottom of unit if separate lid). |
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The manufacturer's product code of the animal housing unit (or bottom of unit if separate lid). |
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The manufacturer's product name of the animal housing unit lid. |
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The manufacturer's product code of the animal housing unit lid. |
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The number of animals in a single housing (e.g., in a single cage, or in an animal carrier for imaging). |
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The sex of multiple animals contained in a single housing (cage). |
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A group consisting of individuals of both sexes (both males and females). E.g., a group of animals in a cage, group of animal handlers. |
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The total period of time that a subject spends in specified housing conditions. |
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The period of time between episodes of manual handling of the subject. |
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A description of the manner in which the housing unit is moved (e.g., how a cage is transported). |
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Whether or not the housing unit (e.g., cage) is individually ventilated. |
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How frequently the entire volume of air within a defined space is replaced (e.g., within an animal cage). |
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Whether or not the housing unit has been previously used for different animals. |
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The device (e.g., animal housing unit aka. cage) has not previously been used for different animals. |
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The device (e.g., animal housing unit aka. cage) has previously been used for different animals. |
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Material provided to enrich the environment of a small animal for the purpose of reducing stress, improving health and/or improving reproducibility of results. E.g., nesting material. |
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The manufacturer of the material provided to enrich the environment of a small animal. |
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Whether or not material is provided to enrich the environment of a small animal for the purpose of reducing stress, improving health and/or improving reproducibility of results. E.g., nesting material. |
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The type of shelter provided for small animals within their housing. |
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The manufacturer's product name of the small animal shelter. |
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The manufacturer's product code of the small animal shelter. |
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Temperature is regulated by feedback from a temperature sensor used to control an active heating or cooling device. |
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The total duration of single light-dark cycle (e.g., usually 24 hours). |
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A device for measuring the temperature of the carrier (holder) used for small animal imaging as a means of monitoring or regulating the animal's temperature (e.g., a non-magnetic thermocouple embedded in or attached to the carrier for MRI). |
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A method or device that uses forced hot air to maintain the body temperature of a subject. |
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An imaging device that contains an integrated method of temperature regulation for maintaining the body temperature of the imaging subject. |
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A device that physically supports the patient and contains an integrated method of temperature regulation for maintaining the body temperature of the imaging subject (e.g., the carrier used for imaging a small animal such as a mouse). |
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A blanket that uses circulating hot water to maintain the body temperature of a subject. |
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A pad that is pre-heated before use that is used to maintain the body temperature of a subject (e.g., pre-heated in a microwave or autoclave). |
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No mechanism is used to maintain the body temperature of a subject. |
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NIH Open Formula Rat and Mouse Ration - 18% Crude Protein Autoclavable. Specification at http://www.ors.od.nih.gov/sr/dvr/Documents/SSFiles/nih31-137j2004.pdf. |
|||
Water that has been purified by reverse osmosis and HCl acidified. |
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Information about different anesthesia methods used during a procedure (from AQI Schema AnesthesiaMethodSetType; see http://www.aqihq.org/qcdrDataSample/prodFiles/2018%20Files/AQISchDoc/AnesthesiaMethodSetType.html). |
|||
Information about a single anesthesia method used during a procedure (from AQI Schema AnesthesiaMethodType; see http://www.aqihq.org/qcdrDataSample/prodFiles/2018%20Files/AQISchDoc/AnesthesiaMethodType.html). |
|||
Category of anesthesia technique used during a procedure (from AQI Schema AnesthesiaCategoryCodeType; see http://www.aqihq.org/qcdrDataSample/prodFiles/2018%20Files/AQISchDoc/AnesthesiaCategoryCodeType.html). |
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Details of anesthesia technique used during a procedure (from AQI Schema AnesthesiaMethodType; see http://www.aqihq.org/qcdrDataSample/prodFiles/2018%20Files/AQISchDoc/AnesthesiaMethodType.html). |
|||
Information about airway management used during a procedure (from AQI Schema AirwayManagementSetType; see http://www.aqihq.org/qcdrDataSample/prodFiles/2018%20Files/AQISchDoc/AirwayManagementSetType.html). |
|||
Type of airway management used during a procedure (from AQI Schema AirwayManagementMethodCodeType; see http://www.aqihq.org/qcdrDataSample/prodFiles/2018%20Files/AQISchDoc/AirwayManagementMethodCodeType.html). |
|||
Subtype of airway management of airway management used during a procedure (from AQI Schema AirwayManagementSubMethodCodeType; see http://www.aqihq.org/qcdrDataSample/prodFiles/2018%20Files/AQISchDoc/AirwayManagementSubMethodCodeType.html). |
|||
Set of medications applied during the anesthesia (from AQI Schema MedicationsSetType; see http://www.aqihq.org/qcdrDataSample/prodFiles/2018%20Files/AQISchDoc/MedicationsSetType.html). |
|||
A gas that delivers an inhalational anesthetic to a subject (e.g., air, oxygen). |
|||
A room for keeping and raising animals for observation or research (vivarium). |
|||
A room for preparing a subject (such as a research small animal) prior to a procedure (such as an imaging procedure). |
|||
A product that is locally manufactured (i.e., within the facility or institution). |
|||
A food item that is out of the ordinary and provides pleasure. |
|||
A substance from a source external to a subject. E.g., a homograft or xenograft (including tumor cells or tissue), fibrils, viruses, cytokines or toxins. |
|||
The tissue from which a substance originated. E.g., the tissue or organ from which a homograft or xenograft (including tumor cells or tissue) was obtained. |
|||
The taxonomic rank value (e.g., genus, subgenus, species or subspecies) from which a substance originated. E.g., the species of animal from which a homograft or xenograft (including tumor cells or tissue) was obtained. |
|||
An identifier of a group of animals that is genetically uniform. |
|||
A description of a group of animals that is genetically uniform. |
|||
A system of names or descriptions used in a particular field. |
|||
An identifier of a specific variation of a targeted gene or introduced transgene. |
|||
A description of a specific variation of a targeted gene or introduced transgene. |
|||
The three dimensional coordinates that identify a (usually small) target within the body. E.g., for the purpose of ablation, biopsy, lesion, injection, stimulation, implantation or radiosurgery. |
|||
The part of the imaging target that was used as a reference point associated with a specific Frame of Reference. The Position Reference Indicator may or may not coincide with the origin of the fixed frame of reference related to the Frame of Reference. For a Patient-related Frame of Reference, this is an anatomical reference point, often a well-known surface anatomical point. |
|||
Tumor cells or tissue or other material obtained from a donor intended to be implanted in a research subject. |
|||
The kidney of an embryo. E.g., used as the source of human embryonic kidney cell lines, though the concept is not specifically human. |
|||
An iodine containing X-Ray contrast agent that does not dissociate in water, therefore, is lower in osmolality, and has a significantly lower incidence of adverse reactions than ionic iodinated contrast agents. |
Replaced by (RID38696, RADLEX, "Non-ionic iodinated contrast agent"). Replaces (96388005, SCT, "Non-ionic iodinated contrast agent"), which is retired in SNOMED CT (Duplicate). |
||
Unrestricted motion of a heart valve. E.g., a prolapsing mitral valve leaflet may be classified as non-flail or flail (abnormal leaflet coaptation or ruptured chordae). |
|||
A nuclear medicine imaging procedure using a single photon emissive radionuclide with tomographic reconstruction, over an anatomical extent of the entire body. |
|||
A nuclear medicine imaging procedure using a single photon emissive radionuclide with tomographic reconstruction combined with transmissive X-Ray computed tomography for attenuation compensation, over an anatomical extent of the entire body. |
|||
The imaging study to be read involves the specified modality |
|||
A final report is a report that is expected to contain all information and all the reportable findings. |
|||
A medical specialty concerned with obstetric and gynecologic imaging. |
|||
Fetal body weight growth percentile estimated from gestational age by method of Campbell 1991. See Campbell WA, Nardi D, Vintzileos AM, Rodis JF, Turner GW, Egan JF. Transverse Cerebellar Diameter/Abdominal Circumference Ratio Throughout Pregnancy: A Gestational Age-Independent Method to Assess Fetal Growth. Obstetrics & Gynecology. 1991;77(6):893-6. Available at: http://journals.lww.com/greenjournal/Fulltext/1991/06000/Transverse_Cerebellar_Diameter_Abdominal.19.aspx. |
Replaces the use of LN:33183-5. |
||
Fetal body weight growth percentile estimated from gestational age by method of Hadlock 1991. See Hadlock FP, Harrist RB, Martinez-Poyer J. In utero analysis of fetal growth: a sonographic weight standard. Radiology. 1991 Oct 1;181(1):129-33. DOI:10.1148/radiology.181.1.1887021. Available at: http://dx.doi.org/10.1148/radiology.181.1.1887021. |
Replaces the incorrect use of LN:33183-5. |
||
A plane passing through the superior extent (i.e., towards the head) of the referenced feature |
|||
A plane passing through the inferior extent (i.e., towards the feet) of the referenced feature |
|||
A plane passing through the proximal extent (i.e., towards the torso) of the referenced feature |
|||
A plane passing through the distal extent (i.e., towards the end of the extremity) of the referenced feature |
|||
A plane passing through the medial extent (i.e., towards the midline of the body) of the referenced feature |
|||
A plane passing through the lateral extent (i.e., away from the midline of the body) of the referenced feature |
|||
A plane passing through the leftmost extent of the referenced feature |
|||
A plane passing through the rightmost extent of the referenced feature |
|||
A plane passing through the anterior extent of the referenced feature |
|||
A plane passing through the posterior extent of the referenced feature |
|||
A plane passing approximately through the center of the referenced feature |
|||
The geometric center point of a feature, such as an organ, implanted device or morphologic anomaly. |
|||
The center of mass of a feature, such as an organ, implanted device or morphologic anomaly |
|||
Point in an image or space from which segmentation is initiated, e.g., by region growing. |
|||
Point in an image or space that is representative (serves as an example or type for others of the same classification) of a feature, such as an organ, implanted device or morphologic anomaly. |
|||
Point in an image or space on the boundary of a feature, such as an organ, implanted device or morphologic anomaly. |
|||
The procedure is contraindicated for patients with impaired renal function. |
|||
Positioning the patient based on alignment of laser cross-hairs. |
|||
Organizational department or section responsible for Abdominal Radiology |
|||
Organizational department or section responsible for Biomedical Engineering |
|||
Organizational department or section responsible for Cardiovascular Radiology |
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Organizational department or section responsible for Information Technology |
|||
Organizational department or section responsible for Medical Physics |
|||
Organizational department or section responsible for Musculoskeletal Radiology |
|||
Organizational department or section responsible for Pediatric Radiology |
|||
Organizational department or section responsible for Thoracic Radiology |
|||
Instances available as input for a general radiotherapeutic workflow. |
|||
Instances created for prescription of a radiotherapeutic treatment. |
|||
Image instances that represent an image series that is intended to be the primary input for the dose calculation. Any parameters required for dose calculation (such as electron density) is derived from this series. |
|||
Image instances that represent an image series from which the display coordinate system for a radiotherapeutic treatment planning is derived. Typically this series does not provide the parameters required for the dose calculation. |
|||
Instances created during the simulation of a radiotherapeutic treatment delivery session. May also include input objects actually used. |
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Instances created during the planning of a radiotherapeutic treatment. May also include input objects actually used. |
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Instances created during the creation of the dosimetric result of a radiotherapeutic treatment plan. May also include input objects actually used. |
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Instances created during the verification of the patient’s treatment position. May also include input objects actually used. |
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Instances created during the treatment session. May also include input objects actually used. |
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Instances created during a treatment course. May also include input objects actually used. |
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Instances created during evaluation of the treatment delivery quality. May also include input objects actually used. |
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Instances available for prescribing a radiotherapeutic treatment delivery. |
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Instances available for creating a radiotherapeutic treatment plan. |
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Instances available to combine radiotherapeutic plans or doses. |
|||
Instances available to perform quality assurance of a radiotherapeutic treatment delivery plan. |
|||
Instances available to perform quality assurance of one of the hardware or software components involved in a radiotherapeutic treatment delivery. |
|||
Instances available for verification of the patient treatment position. |
|||
Instances available for submission for a clinical trial study. |
|||
Instances used as an input of a general radiotherapeutic workflow. |
|||
Instances used for prescribing a radiotherapeutic treatment delivery. |
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Instances used to perform quality assurance of a radiotherapeutic treatment delivery plan. |
|||
Instances used to perform quality assurance of one of the hardware or software components involved in a radiotherapeutic treatment delivery. |
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Instances used during verification of the patient treatment position. |
|||
Real world value map used as the source for derivation. E.g., the map applied to source images before processing them, such as for a threshold based segmentation operation. |
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Segmentation used as the source for derivation. E.g., the binary segmentation that was converted to a labelmap segmentation, or vice versa. |
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Name of an MR pulse sequence for annotation purposes. Potentially vendor-specific name. |
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OCT angiography method that de-correlates the amplitudes between two consecutive B-scans from the narrowed spectral bands was computed, and all the decorrelation values within certain repeated B-scans were averaged to visualize blood vessels. Methods and algorithms for optical coherence tomography-based angiography: a review and comparison. Anqi Zhang ; Qinqin Zhang ; Chieh-Li Chen ; Ruikang K. Wang (2015). See http://biomedicaloptics.spiedigitallibrary.org/article.aspx?articleid=2464650#QuantitativeComparisons. |
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OCT angiography method based on variations in the complex (amplitude and phase) OCT signal from repeated B-scans at the same location. There are a number of factors that may cause a change in the OCT signal frequency relative to the signal due to static tissue background. These factors include, for example, the Doppler effect that induces optical frequency shift and the change in backscattering due to the particles that are moving in and out of the OCT-probe volume during imaging. The changes in signal frequency cause the changes in both the amplitude and the phase of the OCT signal. Comparison of the complex (amplitude and phase) signal from repeated B-scans at the same location provides an image that has higher contrast in areas of erythrocyte motion. This method is referred to as OCT-based micro-angiography - complex (OMAGC). |
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OCT angiography method that analyzes the temporal or spatial statistics of the intensity of speckle from OCT images and identifies blood vessels. |
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OCT angiography method that differentiates flow regions. Static regions usually have high correlation values while flow regions have lower correlation values. |
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OCT angiography method that utilizes the Doppler phase resolved information to provide the velocity of flow. Sometimes referred to as the phase variance method. |
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Image using pseudo colors to illustrate multiple OPTENF images obtained at various depth levels within the retina from the OPT flow volume. |
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Image using pseudo colors to illustrate multiple OPTENF images obtained at various depth levels within the retina from the OPT structural volume. |
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Image that illustrates the vasculature flow within the entire retina. Generated from the OPT flow volume with pixels approximately from inner limiting membrane (ILM) to photoreceptor inner segment/ellipsoid region (ISe). |
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Image that illustrates the OCT structural reflectance within the entire retina. Generated from the OPT structural volume with pixels approximately from inner limiting membrane (ILM) to photoreceptor inner segment/ellipsoid region (ISe). |
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Image that illustrates the vasculature flow within the vitreous. Generated from the OPT flow volume with pixels approximately from a selected location anterior to ILM, to ILM. This space/potential space is referred clinically as the Vitreo-retinal Interface (VRI). |
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Image that illustrates the OCT structural reflectance within the vitreous. Generated from the OPT structural volume with pixels approximately from a selected location that is anterior to ILM, to ILM. This space/potential space is referred clinically as the Vitreo-retinal Interface (VRI). |
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Image that illustrates the OCT vasculature flow within the RNFL around the optic disk. Generated from the OPT flow volume with pixels approximately from ILM to the outer boundary of the RNFL. |
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Image that illustrates the OCT structural reflectance within the RNFL around the optic disk. Generated from the OPT structural volume with pixels approximately from ILM to the outer boundary of the RNFL. |
|||
Image that illustrates the vasculature flow within the anterior layers of retina. Generated from the OPT flow volume with pixels approximately from ILM to ganglion cell layer/inner plexiform layer (GCL/IPL). |
|||
Image that illustrates the OCT structural reflectance within the anterior layers of retina. Generated from the OPT structural volume with pixels approximately from ILM to ganglion cell layer/inner plexiform layer (GCL/IPL). |
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Image that illustrates the vasculature flow in the capillaries that connect the superficial and deeper capillary beds. Generated from the OPT flow volume with pixels approximately at the level of the IPL. Sometimes referred to as the intermediate retina flow. |
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Image that illustrates the OCT structural reflectance in the capillaries that connect the superficial and deeper capillary beds. Generated from the OPT structural volume with pixels approximately at the level of the IPL. Sometimes referred to as the intermediate retina flow. |
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Image that illustrates the vasculature flow at the level of the plexiform layers within the retina. Generated from the OPT flow volume with pixels approximately from inner plexiform layer (IPL) to outer plexiform layer (OPL). |
|||
Image that illustrates the structural reflectance at the level of the plexiform layers within the retina. Generated from the OPT structural volume with pixels approximately from inner plexiform layer (IPL) to outer plexiform layer (OPL). |
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Image that illustrates the vasculature flow at the level of the posterior layers of the retina (outer retina). Generated from the OPT flow volume with pixels approximately in the translucent layers, from OPL to ISe. Sometimes referred to as flow in the deep avascular structure. Note For normal eyes, this image would not show detectable vascular flow. |
|||
Image that illustrates the structural reflectance at the level of the posterior layers of the retina (outer retina). Generated from the OPT structural volume with pixels approximately in the translucent layers, from OPL to ISe. |
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Image that illustrates the vasculature flow at the level of the chroriocapillaris. Generated from the OPT flow volume with pixels approximately below the retinal pigment epithelium (RPE) encompassing the thickness of choriocapillaris. |
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Image that illustrates the structural reflectance at the level of the chroriocapillaris. Generated from the OPT structural volume with pixels approximately below the retinal pigment epithelium (RPE) encompassing the thickness of choriocapillaris. |
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Image that illustrates the vasculature flow at the level of the choroid. Generated from the OPT flow volume with pixels approximately below RPE, encompassing the thickness of choroid. |
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Image that illustrates the structural reflectance at the level of the choroid. Generated from the OPT structural volume with pixels approximately below RPE, encompassing the thickness of choroid. |
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Image that illustrates the vasculature flow at the entire posterior segment, including retina and choroid. Generated from the OPT flow volume with pixels encompassing the entire OCT scan. |
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Image that illustrates the structural reflectance from the entire posterior segment, including retina and choroid. Generated from the OPT structural volume with pixels encompassing the entire OCT scan. |
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A series of densely spaced, parallel B-scans of the same length covering an area. |
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A series of sparsely spaced, parallel B-scans of the same length covering an area. |
|||
A series of B-scans arranged in a radial pattern of the same length covering an area. |
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A pair of horizontal and vertical B-scans in a cross pattern. |
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A series of concentric circular pattern B-scans with various diameters. |
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A series of concentric circular pattern B-scans with various diameters combined with a series of raster B-scan patterns. |
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A series of concentric circular pattern B-scans with various diameters combined with a series of radial B-scan patterns. |
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Retinal surface located approximately at the outer boundary of the retinal nerve fiber layer (RNFL). |
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Retinal surface approximately at the outer boundary of the Ganglion Cell Layer (GCL). |
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Retinal surface located approximately at the outer boundary of the Inner Plexiform Layer (IPL). |
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Retinal surface located approximately at the outer boundary of the Inner Nuclear Layer (INL). |
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Retinal surface located approximately at the outer boundary of the Outer Plexiform Layer (OPL). |
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Retinal surface located approximately at the outer boundary of the Henle Fiber Layer (HFL) when present. |
|||
Surface between Inner and Outer Segments of the photoreceptors |
Retinal surface approximately located at the boundary between the Inner Segments and Outer Segments of the photoreceptors. |
||
Retinal surface located approximately at the retina-RPE interdigitation zone when present. |
|||
Segmentation surface located approximately at the center of the Retinal Pigment Epithelium (RPE). |
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Retinal surface located approximately at the outer boundary of the Bruch’s Membrane (BM). |
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Retinal surface located approximately at the choroid-sclera interface (SC). |
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Retinal surface located approximately at the outer boundary of the choriocapillaris (CC). |
|||
OCT angiography method that utilizes a one-sided ratio on a pixel by pixel basis between various combinations of B-scan repetitions. The ratio is inverted when necessary such that values are less than or equal to one. Individual ratio calculations are averaged or combined across eligible frame combinations for each pixel in the OCT image. |
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OCT angiography method that utilizes a one-sided ratio on a pixel by pixel basis between various combinations of B-scan repetitions. The ratio is inverted when necessary such that values are greater than or equal to one. Individual ratio calculations are averaged or combined across eligible frame combinations for each pixel in the OCT image. |
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Image that illustrates the vascular flow within the posterior layers of the retina, approximately from the posterior border of the outer plexiform layer (OPL) to the level of Bruch’s Membrane (BM). For normal eyes, this image would not show detectable vascular flow. |
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Image that illustrates the structural reflectance within the posterior layers of the retina, approximately from the outer plexiform layer (OPL) to the level of Bruch’s Membrane (BM). |
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Image that illustrates the vascular flow within the anterior layers of retina, approximately from the posterior border of the retinal nerve fiber layer (RNFL) to the inner plexiform layer (IPL). |
|||
Image that illustrates the structural reflectance within the anterior layers of retina, approximately from the posterior border of the retinal nerve fiber layer (RNFL) to inner plexiform layer (IPL). |
|||
Image that illustrates the vascular flow within the plexiform layers of the retina, approximately from within the inner Nuclear layer (INL) to posterior border of the outer plexiform layer (OPL) |
|||
Image that illustrates the structural reflectance within the plexiform layers of the retina, approximately from within the Inner Nuclear Layer (INL) to posterior border of the outer plexiform layer (OPL). |
|||
Image that illustrates the vascular flow within the retinal nerve fiber layer (RNFL), approximately from inner limiting membrane (ILM) to the outer boundary of the RNFL. |
|||
Image that illustrates the structural reflectance within the retinal nerve fiber layer (RNFL), approximately from inner limiting membrane (ILM) to the outer boundary of the RNFL. |
|||
Image that illustrates the vascular flow within a volume selected by the user |
|||
Image that illustrates the structural reflectance within a volume selected by the user |
|||
Image that illustrates the vasculature flow within the posterior layers of the retina (including the outer retina), approximately from the posterior boundary of the outer plexiform layer (OPL) to the inner choriocapillaris (CC). |
|||
Image that illustrates the structural reflectance within the posterior layers of the retina (including the outer retina), approximately from posterior boundary of the outer plexiform layer (OPL) to the inner choriocapillaris (CC). |
|||
Inner surface of the retinal ellipsoid zone, also known as the photoreceptor inner segment/outer segment (IS/OS) junction |
|||
Segmentation surface located approximately midway between the inner and outer surfaces of the retinal ellipsoid zone |
|||
Outer surface of the retinal ellipsoid zone, also known as the photoreceptor inner segment/outer segment (IS/OS) junction |
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Report title for the report of estimated absorbed energy from ionizing radiation to a patient. |
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A mathematical description of a patient model for estimating radiation dose that describes or is thought of as having a human form or human attributes. |
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Boundary based representation of the model for the estimation of radiation transport and absorbed dose in materials. |
|||
Normalized Mean Glandular Dose (DgN) is the conversion value used to calculate the absorbed dose from radiation to the fibroglandular tissue component of the breast from the exposure in air. |
|||
Conversion factor for Size Specific Dose Estimate (SSDE) calculations from CTDIvol. |
|||
Scattering of radiation in a direction opposite to that of the incident radiation. |
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The description of the representation of the estimated absorbed energy to an organ, a set of organs or the whole body, e.g., surface segmentation, mesh, parametric map, RT dose , Secondary Capture SOP Instances, etc. |
|||
The form of the representation used to describe the distribution of the radiation dose. |
|||
The methodology and parameters used to estimate the radiation dose to an organ, the whole body or a phantom. |
|||
The type of model used to define the shape, size, location of objects, etc. to represent a patient or phantom for use in radiation transport analysis. |
|||
A simple object (e.g., cylinder) used to model a patient or organ. |
|||
The type of model used to estimate energy transport and absorbed dose in materials. |
|||
A model that uses geometrical shapes for the estimation of radiation transport and absorbed dose in materials. |
|||
A model that uses volumetric elements for the estimation of radiation transport and absorbed dose in materials. |
|||
A model that uses a mesh structure representation for the estimation of radiation transport and absorbed dose in materials. |
|||
A model that uses surfaces of a non-uniform rational B-spline (NURBS) based representation for the estimation of radiation transport and absorbed dose in materials. |
|||
The data from the model used to estimate radiation dose to a patient or organ. |
|||
Rationale or reference to the methodology for the model used in the estimation of radiation dose. |
|||
The demographics for which the patient model used by the radiation dose estimation method is intended. |
|||
The minimum age used in the patient model in the radiation dose estimation method. |
|||
The maximum age used in the patient model in the radiation dose estimation method. |
|||
A material placed in the radiation beam that is used to completely attenuate the beam in a specific region of the field of view. |
|||
Ratio of the absorbed dose at a given depth in tissue to the absorbed dose at the same point in air. |
|||
The parameters used in the algorithms for determining the radiation dose to a patient, organs, or any material. |
|||
Reference to the SOP Instance that describes the parameters and values used in the algorithms for determining the radiation dose to a patient, organs, or any material. |
|||
The sex used in the patient model in the radiation dose estimation method. |
|||
The minimum weight used in the patient model in the radiation dose estimation method. |
|||
The minimum height used in the patient model in the radiation dose estimation method. |
|||
The maximum weight used in the patient model in the radiation dose estimation method. |
|||
The maximum height used in the patient model in the radiation dose estimation method. |
|||
Reference to the Spatial Registration instance or Deformable Spatial Registration instance. |
|||
Name of the method used to register the frame of reference for two or more sets of data. |
|||
A factor used to make an adjustment to a calculation to account for deviations. |
|||
A value used in a mathematical function to create a curve or a function that approximates a set of data. |
|||
A value used to describe the uniformity or composition of data or a material that relates to the same degree of variability. |
|||
The spatial registration used in the patient model in the radiation dose estimation method. |
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Attenuator in the radiation beam that may alter the estimated radiation dose to the patient, organs, or phantoms. |
|||
The type of object in the radiation beam that may alter the estimated radiation dose to the patient, organs, or phantoms. |
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The table a patient is sitting, standing, or lying on and that is in the radiation beam such that it may alter the estimated radiation dose to the patient, organs, or phantoms. |
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The core material of a table a patient is sitting, standing, or lying on and that is in the radiation beam such that it may alter the estimated radiation dose to the patient, organs, or phantoms. |
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The outer shell of a table a patient is sitting, standing, or lying on and that is in the radiation beam such that it may alter the estimated radiation dose to the patient, organs, or phantoms. |
|||
The padding on a table a patient is sitting, standing, or lying on and that is in the radiation beam such that it may alter the estimated radiation dose to the patient, organs, or phantoms. |
|||
Parameters used in mathematical, simulation, or empirical calculations for radiation dose estimation. |
|||
The equivalent material used to estimate the reduction in radiation intensity. |
|||
An explanation of the actual attenuator material used in the estimation of radiation dose. |
|||
The thickness of a specified material that provides the same attenuation as the actual attenuator. |
|||
The stored data from the model used to represent the X-Ray beam attenuator. |
|||
Model of the attenuator used in the estimation of radiation dose. |
|||
Reference to the methodology or rationale for the model of the beam attenuator used in the estimation of radiation dose. |
|||
The container for the radiation dose estimation methods and parameters. |
|||
Type of method used to estimate the radiation dose to a patient, organs or phantoms. |
|||
Algorithms that use mathematical models that have a deterministic result. |
|||
Algorithms that use mathematical models that use parameters derived from observation. |
|||
A reference to the methodology or rationale for the estimation methodology used for the estimation of radiation dose. |
|||
Representation of radiation dose of equal intensity as a surface, curve, or line. |
|||
Representation of radiation dose intensity at the surface on the skin. |
|||
Representation of the change in radiation dose with respect to the change in another variable. Often represented as a change with respect to time or distance. |
|||
Material that is in radiation beam that is used to provide physical support to the patient or other objects. |
|||
A model for estimating radiation dose defined from the actual patient anatomy or characteristics. |
|||
The measured amount of energy that is deposited in a material by ionizing radiation. |
|||
A computational representation of a human body or other object used to simulate the attenuation of radiation in human tissue. |
|||
A reference to the methodology used to determine the uncertainty in the estimation of radiation dose. |
|||
Absorbed dose to a tissue or organ multiplied by a quality factor to normalize the dose to the type of radiation that is depositing the dose. |
|||
A factor that is used to make an adjustment to a calculation to normalize the data. |
|||
A factor that is used to make an adjustment to a calculation to translate or move the data in a defined manner. |
|||
The amount of a specific tissue content, either mass or volume, in a material. |
|||
A correction factor for a measurement of distance or location. |
|||
A numerical ratio to express a measurement from one unit to another unit. |
|||
The absorbed radiation dose value estimated that occurs most frequently. |
|||
The average value of the equivalent radiation dose estimated. |
|||
The equivalent radiation dose value estimated that occurs most frequently. |
|||
The central value of the equivalent radiation dose estimated. |
|||
This acquisition of data (e.g., for constructing an image) is a repeat of an earlier acquisition that was for some reason unsatisfactory. |
|||
The reason that data (e.g., for constructing an image) was acquired again. |
|||
The acquired data is unsatisfactory because the patient moved. |
|||
The acquired data is unsatisfactory because the contrast timing was not adequate. |
|||
The protocol is appropriate for the indications recorded in the protocol instance. |
The American Academy of Orthopaedic Surgeons (AAOS) defines an appropriate procedure as one for which the expected health benefits exceed the expected health risks by a wide margin. |
||
The protocol is consistent with the regulatory product labeling of the device recorded in the protocol instance. |
|||
The protocol is approved for use at the institution recorded in the protocol instance. |
|||
The protocol is approved for use in the clinical trial recorded in the protocol instance. |
|||
The protocol is specifically approved for use on pregnant patients. |
|||
The protocol is appropriate for execution on the device recorded in the protocol instance (which may identify an individual device by serial number or may identify a family of devices). I.e. the protocol has incorporated model-specific parameters and optimizations as necessary. |
|||
The protocol specifies parameters that are within the operational limits of the device recorded in the protocol instance. I.e. execution of the protocol is not expected to damage or exceed the operational limits of the device. |
|||
The protocol is optimized for the characteristics of the specific instance of the device recorded in the protocol instance. I.e. the protocol has incorporated model-specific parameters and optimizations as necessary. |
|||
The protocol is explicitly disapproved, or approval of the protocol has been withdrawn. |
|||
The protocol is no longer to be used. E.g. it has been replaced by another protocol. |
|||
The protocol is approved for use in experimental procedures. |
|||
The protocol is disapproved for use in experimental procedures. |
|||
The protocol is understood to be eligible for reimbursement by a given payer. |
|||
The protocol is understood to be eligible for reimbursement on a per patient basis by a given payer. |
|||
The protocol is understood to be ineligible for reimbursement by a given payer. |
|||
The protocol is explicitly disapproved for use on pregnant patients. |
|||
The protocol is inappropriate for execution on the device recorded in the protocol instance (which may identify an individual device by serial number or may identify a family of devices). |
|||
The protocol specifies parameters that are not within the operational limits of the device recorded in the protocol instance. I.e. execution of the protocol may damage or exceed the operational limits of the device. |
|||
The protocol is not optimized for the characteristics of the specific instance of the device recorded in the protocol instance. |
|||
The protocol is inappropriate for the indications recorded in the protocol instance. |
The American Academy of Orthopaedic Surgeons (AAOS) defines an appropriate procedure as one for which the expected health benefits exceed the expected health risks by a wide margin. |
||
The protocol is inconsistent with the regulatory product labeling of the device recorded in the protocol instance. |
|||
The protocol is disapproved for use at the institution recorded in the approval instance. |
|||
The protocol is disapproved for use in the clinical trial recorded in the protocol instance. |
|||
The chair of a committee tasked with reviewing and approving protocols in the organization. |
|||
The administrative head of a department that provides radiology services. |
|||
The senior ranking radiologic technologist in the organization. |
|||
A representative of a committee tasked with reviewing and approving protocols in the organization. |
|||
A representative of a committee tasked with evaluating medical ethics. E.g. Institutional Review Board. |
|||
A volume of gel that changes physical characteristics when exposed to ionizing radiation. |
|||
A number of semiconductor devices that generates current when exposed to ionizing radiation. The devices are arranged systematically in a regular pattern. |
|||
A number of devices that measures charge from the ions produced in a medium when exposed to ionizing radiation. The devices are arranged systematically in a regular pattern. |
|||
A semiconductor device that generates current when exposed to ionizing radiation. |
|||
Optically Stimulated Luminescent Dosimeter. It is a crystal that when exposed to green light, emits blue light in proportion to the amount of ionizing radiation it has been exposed to. |
|||
A device that measures charge from the ions produced in a medium when exposed to ionizing radiation. |
|||
A radiophotoluminescence glass dosimeter. It is a solid state cumulative radiation dosimeter usually made of silver-activated phosphate glass. The silver atoms act as radiophotoluminescence centers excited by ionizing radiation. The number of centers excited is proportional to the absorbed dose to the RPLGD. |
|||
Instances that have been selected for export to a teaching file. |
|||
Instances that have been selected for export for a clinical trial. |
|||
The title of a document containing additional teaching file information. |
|||
Instances that have been selected for export to a research collection. |
|||
Instances that have been selected for export for publication. |
|||
The category that describes the subject matter of a teaching file. E.g., a selection from the American Board of Radiology (ABR) subject headings. |
|||
The level of difficult that the material represents. E.g., advanced. |
|||
The teaching material is of an intermediate level of difficulty. |
|||
The teaching material is of an advanced level of difficulty. |
|||
The subject matter pertains to vascular and interventional imaging. |
|||
The entire Human Readable Form of the Unique Device Identifier as defined by the Issuing Agency. |
|||
An offset in time from a particular event of significance. In the context of a clinical trial, this is often the time since enrollment, or the baseline imaging study. |
|||
A well-known landmark of the equipment that is visible by the operator. |
|||
An equipment landmark on the X-Ray Table head located on the table top plane, centered in the left-right direction of the table. |
|||
The X coordinate of the Equipment Landmark in the Table Coordinate System. |
|||
The Z coordinate of the Equipment Landmark in the Table Coordinate System. |
|||
A patient fiducial used to establish the patient location relative to equipment. |
|||
The distance in the Z direction from the Equipment Landmark to the Patient Location Fiducial in the Table Coordinate System. Positive when the direction from the Equipment Landmark to the Patient Location Fiducial lies in the positive Z direction. |
|||
Angle in the XY plane of the isocenter reference system between the Y axis and a plane containing the Z axis and the X-Ray center beam (deg). |
Corresponds to Positioner Isocenter Primary Angle (0018,9463). |
||
Angle, in the plane containing the Z axis of the isocenter reference system and the X-Ray center beam, between the XY plane and the X-Ray center beam (deg). |
Corresponds to Positioner Isocenter Secondary Angle (0018,9464). |
||
Corresponds to Positioner Isocenter Detector Rotation Angle (0018,9465). |
|||
Position of the X-Ray center beam in the isocenter reference system in the X direction (deg) at the end of an irradiation event. |
|||
Position of the X-Ray center beam in the isocenter reference system in the Z direction (deg) at the end of an irradiation event. |
|||
Rotation of the X-Ray detector plane (deg) at the end of an irradiation event. |
See (128759, DCM, "Positioner Isocenter Detector Rotation Angle"). |
||
Angle of the head-feet axis of the table (deg) relative to the horizontal plane at the end of an irradiation event. |
|||
Rotation of the table in the horizontal plane (deg) at the end of an irradiation event. |
|||
Angle of the left-right axis of the table (deg) relative to the horizontal plane at the end of an irradiation event. |
|||
X position of the Table Reference Point with respect to the Isocenter (mm). |
|||
Y position of the Table Reference Point with respect to the Isocenter (mm). |
|||
Z position of the Table Reference Point with respect to the Isocenter (mm). |
|||
X position of the Table Reference Point with respect to the Isocenter (mm) at the end of an irradiation event. |
|||
Y position of the Table Reference Point with respect to the Isocenter (mm) at the end of an irradiation event. |
|||
Z position of the Table Reference Point with respect to the Isocenter (mm) at the end of an irradiation event. |
|||
The anatomical feature or point of reference on which the reference location is based. |
|||
Characterizes the geometry of the reference location (e.g., a plane or point). |
|||
Login name (user ID) of human observer who created the observations. |
|||
The tabulation of gray level run lengths in a particular direction in an image. Abbreviated GLRLM. See [IBSI Features]. |
|||
A tabulation of counts of the number of groups of connected voxels with a specific discretized gray level value and size. Abbreviated GLSZM. See [IBSI Features]. |
|||
A tabulation of counts of the number of groups (or zones) of linked voxels that share a specific discretised grey level value and possess the same distance to ROI edge. Abbreviated GLDZM. See [IBSI Features]. |
|||
A matrix containing the sum of grey level differences of pixels/voxels with a discretised grey level and average discretised grey level of neighbouring pixels/voxels within a specified Chebyshev distance. Abbreviated NGTDM. See [IBSI Features]. |
|||
A tabulation of the counts of dependent (within a specified coarseness parameter) neighbouring discretised grey levels within a specified Chebyshev distance. Abbreviated NGLDM. See [IBSI Features]. |
|||
The probability corresponding to the most common gray level co-occurrence in the GLCM. Abbreviated MAX. See Fcm.joint.max in [IBSI Features]. |
|||
The gray level weighted sum of joint probabilities of a Gray Level Co-occurrence Matrix (GLCM). See Fcm.joint.avg in [IBSI Features]. |
|||
The sum of squares of the difference from the joint average of a Gray Level Co-occurrence Matrix (GLCM). See Fcm.joint.var in [IBSI Features]. |
|||
The average for the diagonal probabilities of a Gray Level Co-occurrence Matrix (GLCM). See Fcm.diff.avg in [IBSI Features]. |
|||
The variance for the diagonal probabilities of a Gray Level Co-occurrence Matrix (GLCM). See Fcm.diff.var in [IBSI Features]. |
|||
The entropy for the diagonal probabilities of a Gray Level Co-occurrence Matrix (GLCM). See Fcm.diff.entr in [IBSI Features]. |
|||
The average for the cross-diagonal probabilities of a Gray Level Co-occurrence Matrix (GLCM). See Fcm.sum.avg in [IBSI Features]. |
|||
The variance for the cross-diagonal probabilities of a Gray Level Co-occurrence Matrix (GLCM). See Fcm.sum.var in [IBSI Features]. |
|||
The entropy for the cross-diagonal probabilities of a Gray Level Co-occurrence Matrix (GLCM). See Fcm.sum.entr in [IBSI Features]. |
|||
The inverse difference of a Gray Level Co-occurrence Matrix (GLCM). See Fcm.inv.diff in [IBSI Features]. |
Sometimes referred to as "homogeneity" but that term is historically used to refer to the "inverse difference moment", which is calculated from the square of differences rather than absolute value of them. |
||
The normalized inverse difference of a Gray Level Co-occurrence Matrix (GLCM). See Fcm.inv.diff.norm in [IBSI Features]. |
The US not UK spelling of "normalized" is used to be consistent with the DICOM convention, rather than the IBSI spelling. Replaced by (NDRX, IBSI, "Normalized Inverse Difference of GLCM"). |
||
The normalized inverse difference moment of a Gray Level Co-occurrence Matrix (GLCM). See Fcm.inv.diff.mom.norm in [IBSI Features]. |
The US not UK spelling of "normalized" is used to be consistent with the DICOM convention, rather than the IBSI spelling. Replaced by (1QCO, IBSI, "Normalized Inverse Difference Moment of GLCM"). |
||
The inverse variance of a Gray Level Co-occurrence Matrix (GLCM). See Fcm.inv.var in [IBSI Features]. |
|||
The autocorrelation of a Gray Level Co-occurrence Matrix (GLCM). See Fcm.auto.corr in [IBSI Features]. |
|||
The cluster tendency of a Gray Level Co-occurrence Matrix (GLCM). See Fcm.clust.tend in [IBSI Features]. |
|||
The cluster shade of a Gray Level Co-occurrence Matrix (GLCM). See Fcm.clust.shade in [IBSI Features]. |
|||
The cluster prominence of a Gray Level Co-occurrence Matrix (GLCM). See Fcm.clust.prom in [IBSI Features]. |
|||
The first measure of information correlation of a Gray Level Co-occurrence Matrix (GLCM). See Fcm.info.corr.1 in [IBSI Features]. |
Replaced by (R8DG, IBSI, "First Measure of Information Correlation of GLCM"). |
||
The second measure of information correlation of a Gray Level Co-occurrence Matrix (GLCM). See Fcm.info.corr.2 in [IBSI Features]. |
Replaced by (JN9H, IBSI, "Second Measure of Information Correlation of GLCM"). |
||
A measure of the distribution of short runs in a gray level run length matrix. Abbreviated SRE. See Frlm.sre in [IBSI Features]. |
|||
A measure of the distribution of long runs in a gray level run length matrix. Abbreviated LRE. See Frlm.lre in [IBSI Features]. |
|||
A measure of the distribution of low gray level values in a gray level run length matrix. Abbreviated LGRE. See Frlm.lgre in [IBSI Features]. |
|||
A measure of the distribution of high gray level values in a gray level run length matrix. Abbreviated HGRE. See Frlm.hgre in [IBSI Features]. |
|||
A measure of the joint distribution of short runs and low gray level values in a gray level run length matrix. Abbreviated SRLGE. See Frlm.srlge in [IBSI Features]. |
Replaced by (HTZT, IBSI, "Short Run Low Gray Level Emphasis"). |
||
A measure of the joint distribution of short runs and high gray level values in a gray level run length matrix. Abbreviated SRHGE. See Frlm.srhge in [IBSI Features]. |
Replaced by (GD3A, IBSI, "Short Run High Gray Level Emphasis"). |
||
A measure of the joint distribution of long runs and low gray level values in a gray level run length matrix. Abbreviated LRLGE. See Frlm.lrlge in [IBSI Features]. |
Replaced by (IVPO, IBSI, "Long Run Low Gray Level Emphasis"). |
||
A measure of the the joint distribution of long runs and high gray level values in a gray level run length matrix. Abbreviated LRHGE. See Frlm.lrhge in [IBSI Features]. |
Replaced by (3KUM, IBSI, "Long Run High Gray Level Emphasis"). |
||
A measure of the similarity of gray level values throughout the image in a gray level run length matrix. Abbreviated RLM.GLNU. See Frlm.glnu in [IBSI Features]. |
Replaced by (R5YN, IBSI, "Gray Level Nonuniformity in Runs"). |
||
A normalized measure of the similarity of gray level values throughout the image in a gray level run length matrix. See Frlm.glnu.norm in [IBSI Features]. |
The US not UK spelling of "normalized" is used to be consistent with the DICOM convention, rather than the IBSI spelling. Replaced by (OVBL, IBSI, "Normalized Gray Level Nonuniformity in Runs"). |
||
A measure of the the similarity of the length of runs throughout the image in a gray level run length matrix. Abbreviated RLNU. See Frlm.rlnu in [IBSI Features]. |
|||
A normalized measure of the the similarity of the length of runs throughout the image in a gray level run length matrix. See Frlm.rlnu.norm in [IBSI Features]. |
The US not UK spelling of "normalized" is used to be consistent with the DICOM convention, rather than the IBSI spelling. Replaced by (IC23, IBSI, "Normalized Run Length Nonuniformity"). |
||
A measure of the homogeneity and distribution of runs of an image in a specific direction in a gray level run length matrix. Abbreviated RPC. See Frlm.r.perc in [IBSI Features]. |
|||
The variance in runs for the gray levels in a gray level run length matrix. See Frlm.gl.var in [IBSI Features]. |
|||
The variance in runs for run lengths in a gray level run length matrix. See Frlm.rl.var in [IBSI Features]. |
|||
The entropy of runs in a gray level run length matrix. See Frlm.rl.entr in [IBSI Features]. |
|||
A feature that emphasizes small zones from a gray level size zone matrix. Abbreviated SZE. See Fszm.sze in [IBSI Features]. |
|||
A feature that emphasizes large zones from a gray level size zone matrix. Abbreviated LZE. See Fszm.lze in [IBSI Features]. |
|||
A feature that emphasizes low gray level zones from a gray level size zone matrix. Abbreviated LGZE. See Fszm.lgze in [IBSI Features]. |
|||
A feature that emphasizes high gray level zones from a gray level size zone matrix. Abbreviated LGZE. See Fszm.hgze in [IBSI Features]. |
|||
A feature that emphasizes small zone sizes and low gray levels from a gray level size zone matrix. Abbreviated SZLGE. See Fszm.szlge in [IBSI Features]. |
Replaced by (5RAI, IBSI, "Small Zone Low Gray Level Emphasis"). |
||
A feature that emphasizes small zone sizes and high gray levels from a gray level size zone matrix. Abbreviated SZHGE. See Fszm.szhge in [IBSI Features]. |
Replaced by (HW1V, IBSI, "Small Zone High Gray Level Emphasis"). |
||
A feature that emphasizes large zone sizes and low gray levels from a gray level size zone matrix. Abbreviated LZLGE. See Fszm.lzlge in [IBSI Features]. |
Replaced by (YH51, IBSI, "Large Zone Low Gray Level Emphasis"). |
||
A feature that emphasizes large zone sizes and high gray levels from a gray level size zone matrix. Abbreviated LZHGE. See Fszm.lzhge in [IBSI Features]. |
Replaced by (J17V, IBSI, "Large Zone High Gray Level Emphasis"). |
||
The distribution of zone counts over the gray values in a gray level size zone matrix. Abbreviated SZM.GLNU. See Fszm.glnu in [IBSI Features]. |
Replaced by (JNSA, IBSI, "Gray Level Nonuniformity of Size Zone Counts"). |
||
The normalized distribution of zone counts over the gray values in a gray level size zone matrix. See Fszm.glnu.norm in [IBSI Features]. |
The US not UK spelling of "normalized" is used to be consistent with the DICOM convention, rather than the IBSI spelling. Replaced by (Y1RO, IBSI, "Normalized Gray Level Nonuniformity of Size Zone Counts"). |
||
The distribution of zone counts over the different zone sizes in a gray level size zone matrix. Abbreviated ZSNU. See Fszm.zsnu in [IBSI Features]. |
|||
The normalized distribution of zone counts over the different zone sizes in a gray level size zone matrix. See Fszm.zsnu.norm in [IBSI Features]. |
The US not UK spelling of "normalized" is used to be consistent with the DICOM convention, rather than the IBSI spelling. Replaced by (VB3A, IBSI, "Normalized Zone Size Nonuniformity"). |
||
The fraction of the number of realised zones relative to the maximum number of potential zones in a gray level size zone matrix. Abbreviated ZPERC. See Fszm.z.perc in [IBSI Features]. |
|||
The variance ithe variance in zone counts for the gray levels in a gray level size zone matrix. See Fszm.gl.var in [IBSI Features]. |
Replaced by (BYLV, IBSI, "Gray Level Variance in Size Zones"). |
||
The variance in zone counts for the different zone sizes in a gray level size zone matrix. See Fszm.zs.var in [IBSI Features]. |
|||
The entropy of zone sizes in a gray level size zone matrix. See Fszm.zs.entr in [IBSI Features]. |
|||
Person who looks at and interprets medical images against defined criteria for the purpose of establishing eligibility of the subject of said images to be enrolled in a research experiment or a clinical trial. |
|||
Person who designates locations on medical images (such as the location of lesions) for other persons or devices to measure or interpret. E.g., for the purpose of consistent target lesion selection for application of therapeutic response criteria by multiple independent readers. |
|||
Person who reviews medical images to evaluate the compliance of said images with quality criteria. |
|||
Person who reviews results derived from medical images to evaluate the compliance of said results with quality criteria. |
|||
A reference to a predecessor model that has been edited to produce the current model. For example: inclusion of more organs, completion of a partial segmentation, insertion of a bisection plane to allow interior inspection, or addition of support material. |
|||
A reference to a predecessor model that contributed to the creation of the current combined model. This includes simple assembly of discrete pieces as well as more complex combination. For example: by Boolean mathematical and similar operations. |
|||
Intended for educational purposes. For example: patient or care-giver education/informed consent, or training residents and fellows. |
|||
Intended to be used to manufacture a patient-matched tool that is employed during a medical procedure. For example: drill/cutting guides, immobilizers, radiation shields, and plate bending templates. |
|||
Intended to be used to manufacture a fully external prosthetic/orthotic |
|||
Intended to be used to manufacture a wholly or partially internal implant |
|||
Intended to be used for simulation and/or practice of a surgery or other medical procedure. "Simulation" is not used for patient-matched simulation, as this would be covered by "Diagnostic Intent" or "Planning Intent". |
|||
A 3D manufacturing model derived from images from multiple different modalities. |
|||
A 3D manufacturing model derived from measurements made from photographs. |
|||
A 3D manufacturing model derived from laser scanning measurements. |
|||
The fraction of fat present, derived using Dixon or other techniques. |
|||
Water/Fat In Phase signal, derived using Dixon or other techniques. |
|||
Water/Fat Out of phase signal, derived using Dixon or other techniques. |
|||
The fraction of water present, derived using Dixon or other techniques. |
|||
Estimation of the course of fiber tracts by analysis of anisotropic diffusion. |
|||
Images that have been used in the treatment planning process. |
|||
Images that have been used for dose calculation in the treatment planning process. |
|||
Images that are used in a treatment session as reference images to position the patient. |
|||
Registrations that have been used in the treatment planning process |
|||
Registrations that have been created in the execution of a treatment session. |
|||
A marker that receives a radio signal and transmits a response. |
|||
A marker containing a substance that produces a distinctive signal on MR images. |
|||
Infrared reflecting external marker, e.g., attached to skin or stereotactic frame. |
|||
Visible light reflecting external marker, e.g., attached to skin or stereotactic frame. |
|||
The average atomic number for a compound or mixture of materials. There are a variety of methods for estimating this value for a given compound. |
|||
Modified pixel values within the Hounsfield Unit Value range. |
|||
Each real-world value mapped pixel represents a certain value for a specified material (the exact interpretation of the value range has to be defined by the user). |
|||
Each real-world value mapped pixel value represents a property the attenuation of a material such as attenuation, concentration or density. |
|||
Image with the attenuation contribution of one or more materials removed. For pixels that did not contain any of the removed material(s), the pixel values are unchanged. |
|||
Image where pixel values have been modified to highlight a certain target material by partially suppressing the background and/or by enhancing the modified material. |
|||
Image where pixel values have been modified to partially suppress the modified material (opposite to Material Highlighted image). |
|||
Image where pixels are recalculated by a vendor-specific method. |
|||
Each real-world value mapped pixel represents a fraction, by volume, occupied by the material. |
|||
Each real-world value mapped pixel represents a fraction, by mass, occupied by the material. |
|||
An objective to achieve a radiation dose which is greater than or equal to the specified radiation dose at the surface of a volume. |
|||
An objective to achieve a radiation dose which is less than or equal to the specified radiation dose at the surface of a volume. |
|||
An objective to achieve a radiation dose which is greater than or equal to the specified radiation dose throughout a volume. |
|||
An objective to achieve a radiation dose which is less than or equal to the specified radiation dose throughout a volume. |
|||
An objective to achieve a mean radiation dose over the volume which is greater than or equal to the specified radiation dose. |
|||
An objective to achieve a mean radiation dose over the volume which is less than or equal to the specified radiation dose. |
|||
An objective to achieve an equivalent uniform dose (EUD) which is greater than or equal to the specified radiation dose. |
|||
An objective to achieve an equivalent uniform dose (EUD) which is less than or equal to the specified radiation dose. |
|||
An objective to achieve a radiation dose which is equal to the specified radiation dose throughout the volume. |
|||
An objective to achieve a conformity index which is greater than or equal to the specified conformity index for a radiation dose which is equal to the specified radiation dose throughout the volume. Minimum Conformity Index as defined in [Feuvret], page 335. |
|||
An objective to achieve a healthy tissue conformity index which is greater than or equal to the specified healthy tissue conformity index for a radiation dose which is equal to the specified radiation dose throughout the volume. Minimum Healthy Tissue Conformity Index as defined in [Feuvret], page 335. |
|||
An objective to achieve a conformation number which is greater than or equal to the specified conformation number greater for a radiation dose which is equal to the specified radiation dose throughout the volume. Minimum Conformation Number as defined in [Feuvret], page 335. |
|||
An objective to achieve a homogeneity index which is less than or equal to the specified homogenity index for a radiation dose which is equal to the specified radiation dose throughout the volume. Maximum Homogeneity Index as defined in [Feuvret], page 335. |
|||
An objective to achieve a radiation dose which is greater than or equal to the specified radiation dose for at least a specified volume percentage. |
|||
An objective to achieve a radiation dose which is less than or equal to the specified radiation dose for at least a specified "volume percentage. |
|||
An objective to achieve a radiation dose which is greater than or equal to the specified radiation dose for at least a specified volume size. |
|||
An objective to achieve a radiation dose which is less than or equal to the specified radiation dose for at least a specified volume size. |
|||
The specified volume size of an anatomical region in a Dosimetric Objective. |
|||
The percentage which represents a fractional parameter used by a Dosimetric Objective. |
|||
Free text note describing the devices and techniques used to shape the radiation beam. |
|||
Free text note to describe suggestions or advice to treatment planning. |
|||
Free text note describing additional activities that address individual patient needs. |
|||
Free text note describing the process to position the patient for the procedure. |
|||
Free text note describing management of patient motion during the radiation treatment. |
|||
Free text note describing the setup of the patient on the patient support device(s). |
|||
Free text note describing the intended use of images for planning. |
|||
Free text note describing the procedure "for acquiring and applying information about patient position. |
|||
Free text note describing the Quality Assurance Process for the treatment of the patient. |
|||
Particle for a radiotherapeutic treatment using beams of energetic protons, positive ions or other particles. |
|||
Isotope for a radiotherapeutic treatment where a decaying radiation source is placed inside or next to a target area, called Brachytherapy. |
|||
Free text note describing how adaptive radiotherapy is to be performed. |
|||
Isotope for a radiotherapeutic treatment where a decaying radiation source is placed outside the body. |
|||
Volume containing tissues to be irradiated to a specified radiation dose, typically encompassing a tumor, and possibly including surrounding subclinical disease, and margin(s) to account for uncertainties in patient positioning and organ motion. |
|||
Non-target structure or volume used when calculating the radiation dose, e.g., during an optimzation process. This may be a structure whose proximity to the target and/or radiosensitivity restrict the radiation dose deliverable to the target. |
|||
Points or volumes used as spatial references, e.g., treatment or imaging device isocenter or fiducial markers. |
|||
Device used to reproducibly position or limit the motion of a patient or portion of a patient during treatment. |
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Device used to deliver Brachtherapy treatments. This includes both devices containing radioactive sources (seeds, eye plaques) and devices used to position radioactive sources (source applicators, channels etc.). |
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A volume representing the external shape of the patient body used in radiotherapeutic procedures. |
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A volume that does not correspond to an identifiable physical entity and has user specified boundaries. |
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Clinical Target Volume encompassing diseased lymph node(s) , with margin to include surrounding sub-clinical disease as defined in [ICRU Report 50]. |
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Clinical Target Volume encompassing primary tumor(s) , with margin to include surrounding sub-clinical disease as defined in [ICRU Report 50]. |
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Gross Tumor Volume encompassing diseased lymph nodes as defined in [ICRU Report 50]. |
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Gross Tumor Volume encompassing primary tumor(s) as defined in [ICRU Report 50]. |
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Planning Target Volume encompassing a nodal CTV, with margin to account for uncertainty in patient positioning and organ motion as defined in [ICRU Report 50]. |
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Planning Target Volume encompassing a primary CTV, with margin to account for uncertainty in patient positioning and organ motion as defined in [ICRU Report 50]. |
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Entire Body as a target volume for radiotherapy treatment. The usual term for a treatment technique irradiating this target is Full Body Irradiation. |
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Internal Target Volume encompassing the CTV, with margin to account for internal motion, often delineated using multiple images, e.g., acquired over a breathing cycle, cardiac cycle, etc, as defined in [ICRU Report 50]. |
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Volume encompassing the Organ At Risk (Planning organ at Risk Volume (PRV)) with margin to account for uncertainty in patient positioning and organ motion as defined in [ICRU Report 50]. |
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Volume to which delivered radiation dose should be minimized or limited as defined in [ICRU Report 62]. |
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Volume enclosed by an isodose surface appropriate to achieve the purpose of treatment (e.g., tumor eradication or palliation) as defined in [ICRU Report 50]. |
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Normal tissue that receives undesired radiation and may be damaged by the radiation treatment as defined in [ICRU Report 50]. The treatment is typically planned to limit the radiation dose to such an organ. |
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A volume used to express dosimetric constraints for shaping the radiation dose distribution. |
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A volume surrounding the target to achive a high radiation dose gradient using a low radiation dose constraint. |
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A point for which a specific radiation dose value is chosen. The rest of the radiation dose distribution is normalized against" this value. |
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Volume in which the interaction of radiation with matter is taken into account. |
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The external boundary of patient tissue without additional devices. |
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The external boundary of patient tissue plus devices that may be attached or adjacent to the body (such as Bolus, Patient Support Devices, Patient Immobilization Devices). |
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Point at which the patient is initially positioned prior to any other positioning procedure. |
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A reference point used for patient setup based on room lasers. |
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A reference point used for patient setup based on movable lasers. |
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A reference point at which patient position verification references are acquired. |
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The Conformity Index for a Dosimetric Objective as defined in [Feuvret], page 335. |
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The Healthy Tissue Conformity Index for a Dosimetric Objective as defined in [Feuvret], page 335. |
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The Conformation Number for a Dosimetric Objective as defined in [Feuvret], page 335. |
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The Homogeneity Index for a Dosimetric Objective as defined in [Feuvret], page 335. |
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Channel shield device used in brachytherapy treatment delivery |
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A logical combination of two or more volumes for which the combination is not classified. |
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Ratio of the mass density of a material relative to the mass density of water. |
|||
Ratio of the electron density of a material relative to the electron density of water. |
|||
Ratio of effective atomic number to mass (AMU -1) for a material. |
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Ratio of the linear stopping power of a material to the linear stopping power of water. |
|||
An energy value which qualifies a quantity or parameter whose value is defined in respect to this energy. |
|||
Linear Cell Kill Factor (α) as defined in J. Deacon et al (Rad. Onc 2(4) : 317-323, 1984), page 318- |
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Quadratic Cell Kill Factor (β) as defined in J. Deacon et al (Rad. Onc 2(4) : 317-323, 1984), page 318. |
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High Dose Fraction Linear Cell Kill Factor (γ) as defined in Frederick W. McKenna et (J. Med. Phys, 36(2) : 100-106, 2011), page 102. |
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Half-time for Tissue Repair as defined in R Singh R, et al. (Medical Dosimetry 28(4) : 225-259, 2003), page 256. |
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High Dose Fraction Transition Dose as defined in Astrahan, M. (Med. Phys., 35(9) : 4161-4172, 2008), page 4164. |
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The atomic number of an element, i.e. the number of protons found in the nucleus of an atom. |
|||
Tissue-specific parameter that describes the volume effect of radiation dose delivered to a volume. See AAPM Report 166 (http://www.aapm.org/pubs/reports/RPT_166.pdf) for additional information. |
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A treatment consisting of a single treatment fraction, e.g., for stereotactic treatments. |
|||
A treatment consisting of a one treatment fraction per day, typically 1.8-2.0 Gy per treatment fraction. |
|||
A treatment consisting of a reduced number of treatment fractions relative to a standard fractionation, typically with a higher radiation dose per fraction. |
|||
A treatment consisting of an increased number of fractions relative to a standard fractionation, typically two per day with smaller radiation dose per fraction. |
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A treatment consisting of a continuous delivery using a temporary implant. |
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A treatment consisting of a continuous delivery using a permanent implant. |
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A treatment technique in which the field shape and the source position do not change during delivery. |
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A treatment technique in which the field shape does not change during delivery while the source position follows an arc. |
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A treatment technique in which the field shape changes during delivery while the source position follows an arc. |
|||
A treatment technique in which the field shape does not change during an exposure. Several field shapes may be used in different exposures at the same source position. |
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A treatment technique in which the field shape continously changes during an exposure at the same source position. |
|||
A treatment technique in which the field shape, gantry speed and radiation dose rate changes during delivery while the source position follows an arc. |
|||
A treatment technique in which the field shape continously changes during delivery while the source position follows a continous arc in parallel to a simultaneous patient support movement. |
|||
A treatment technique in which the field shape and the source position do not change during" delivery while the patient support is moving. |
|||
A device attached to the tabletop that is also screwed into the skull of the patient's head to position and orient the head in a prescribed geometry relative to the tabletop. The device is commonly known as a "halo". |
|||
A device that is placed over the patient's face and attached to the tabletop to prevent the patient from moving relative to the tabletop. |
|||
A device that is placed over the patient's face and neck and attached to the tabletop to prevent the patient from moving relative to the tabletop. |
|||
A device that is modified by pressure (molded) to fit another object (such as the patient"s anatomy) and then used to control the reproducibility of the patient"s treatment position. |
|||
A device that is fabricated from a mold of another object (like the patient"s anatomy) and then used to control the reproducibility of the patient"s treatment position. |
|||
A device placed on the tabletop to support the chest and arms of a patient in a prescribed position and orientation. |
|||
A device placed beneath a patient to support the whole body in a prescribed position and orientation relative to the table top. |
|||
A device placed beneath a patient to support a body part in a prescribed position and orientation relative to the table top. It is commonly a bag containing low density polystyrene spheres that becomes semi-hard when vacuum is applied conforming to the bottom surface of the patient. |
|||
A device placed beneath a patient to support the whole body in a prescribed position and orientation relative to the table top. It is commonly shaped like a hollow half cylinder. The space between the patient and the wall is commonly filled with a dual component foam that hardens conforming to the bottom surface of the patient. |
|||
A flexible fluid container inserted into the rectum to maintain an immovable geometry during treatment. |
|||
An intracavity cylinder inserted into the vagina to achieve greater radiation dose control and radiation dose shaping. Radioactive sources are inserted into the cylinder for treatment. |
|||
A device, typically made of a low temperature alloy, such as Lipowitz"s metal, that provides an opening in a beam block with constant attenuation across an area of the beam to prevent or reduce radiation dose delivery to normal tissues. |
|||
A device placed into a machine slot or an applicator to which accessories are attached. |
|||
A device placed into a radiotherapy machine slot which provide slot to add other devices and/or to limit the beam. |
|||
A category of methods for the calculation of effective dose that are based on radiation transport and are used to predict the Relative Biological Effectiveness of an ion beam based on the quality of the radiation used. [Wambersie A, RBE, reference RBE and clinical RBE: Applications of these concepts in hadron therapy, Strahlentherapie und Onkologie 1999 June, 175(2) : 39-43] [Paganetti H, et al., Relative biological effectiveness (RBE) values for proton beam therapy, Int J Rad. Onc Biol Phys, 2002 June; 53(2) : 407-421] |
|||
A category of methods for the calculation of effective dose that are based on Fractionation or temporal patterns and are used to predict the Biologically Effective Dose. [Thames HD, Hendry JH. Fractionation in radiotherapy. New York: Taylor & Francis; 1987] [Barendsen, G.W (1982) Dose fractionation, dose rate and iso-effect relationships for normal tissue responses, Int. J. Radiat. Oncol. Biol. Phys. 8 (11) : 1981-1997.] |
|||
The Local Effect Model (LEM) method used to predict the Relative Biological Effectiveness of dose delivered using ion beams. [Grun, R. Friedrich, T. Elasasser, T. Kramer, M. Zink, K. Karger, C. P. Durante, M. Engenhard-Cabillic, R. Scholz, M. (2012) "Impact of enhancements in the local effect model (LEM) on the predicted RBE-weighted target dose distribution in carbon ion therapy" Physics in Medicine and Biology 57: 7261 - 7274.] |
|||
The Microdosimetric Kinetic Model (MKM) " used to predict the Relative Biological Effectiveness of dose delivered using ion beams. [Inaniwa, T. Furukawa, T. Kase, Y. Matsufuji, N. Toshito, T. Matsumoto, Y. Furusawa, Y. Node, K. (2010) "Treatment planning for a scanned carbon beam with a modified microdosimetric kinetic model" Physics in Medicine and Biology 55: 6721 - 6737.] |
|||
The linear quadratic model usedto compute the equivalent Biologically Effective Dose (BED) delivered in 2 Gray dose fractions. [Fowler JF. The linear-quadratic formula and progress in fractionated radiotherapy. Br J Radiol. 1989 Aug; 62 (740) : 679-94.] |
|||
The linear quadratic model usedto compute the equivalent Biologically Effective Dose (BED) delivered at an infinitely low dose-rate. |
|||
The modified linear quadratic model with time factor method usedto compute the equivalent Biologically Effective Dose (BED) delivered at an infinitely low dose-rate, taking into account tumor repopulation during treatment. |
|||
The linear-quadratic-linear dose-response model usedto compute the equivalent Biologically Effective Dose (BED) delivered at an infinitely low dose-rate, taking into account linear cell survival with high dose fractions. |
|||
The linear-quadratic dose-response model modified for low-dose rate brachytherapy used to compute the equivalent Biologically Effective Dose (BED) delivered at an infinitely low dose-rate. |
|||
A Radiotherapy prescription prescribed prior to the current prescription. |
|||
Image Instances available as input for prescribing a Radiotherapy treatment prescription. |
|||
Image Instances available as input for planning a Radiotherapy treatment plan. |
|||
A treatment technique using multiple decaying radiation sources at fixed spatial locations. |
|||
A treatment technique using a robotic delivery device with real-time motion tracking and compensation. |
|||
A treatment technique using a robotic delivery device without real-time motion tracking and compensation. |
|||
The injector device detected a pressure above the warning threshold, generated a warning and did not automatically terminate the administration. |
|||
The injector device detected a pressure above the adjustment limit, took compensating action and did not automatically terminate the administration. |
|||
The injector device detected a flow rate above the warning threshold, generated a warning and did not automatically terminate the administration. |
|||
The injector device detected a flow rate above the adjustment limit, took compensating action and did not automatically terminate the administration. |
|||
The injector device terminated the administration due to detection of an abort request by the operator. |
|||
The device detected that a pause duration has been reached and the device resumed automatically. |
|||
The injector device detected a pressure above the termination limit and automatically terminated the administration. |
|||
The injector device detected a flow rate above the termination limit and automatically terminated the administration. |
|||
The Injector device detected that a pause duration has exceeded limit and the injector device terminated the administration. |
|||
The injector device detected a communication loss and automatically |
|||
The injector device detected an unspecified failure and automatically |
|||
The injector device started saline flow for the purpose of keeping vein open. |
|||
The injector device ended saline flow for the purpose of keeping vein open. |
|||
The injector device detected that a syringe was attached to the injector. |
|||
The injector device detected that a syringe was detached from the injector. |
|||
Total volume of flush delivered by the keep vein open function of the injector. |
|||
An administration phase where fluid is being delivered by an injector system according to the programmed instructions. |
|||
An administration phase where fluid delivery is stopped by the injector system until a programmed time elapses. |
|||
An administration phase where the fluid is delivered automatically by an injector system and stopped under manual control by the operator. |
|||
An administration phase where the fluid is delivered by the injector system under manual control by the operator. E.g., Cardiac Cath. |
|||
Information only available if injection was triggered manually. |
|||
An administration mode where the fluid is delivered by a mechanical injector system. |
|||
An administration mode where the substance is delivered manually E.g., Clinician manual injection of an Imaging Agent or oral consumption by a patient. |
|||
The injector device detected air in the tubing or syringe before or during the Imaging Agent administration and did not automatically terminate the administration. |
|||
The injector device detected air in the tubing or syringe and terminated the administration. |
|||
The injector device received instruction from scanner to terminate the administration and terminated the administration. |
|||
The injector device detected critical battery level and terminated the administration. |
|||
The injector device detected removal of a consumable from the injector device and terminated the administration. |
|||
A code that specifies how the Imaging Agent is administered to the patient. |
|||
A report of the planned patient-specific Imaging Agent administration steps. |
|||
Description of a specific Imaging Agent that was planned or was administered. |
|||
Number of osmoles of solute per kilogram of solvent at 37°C. |
|||
A measure of a resistance of a fluid to gradual deformation by stress, measured at 37°C. |
|||
Indicates if an Imaging Agent was warmed prior to the administration procedure. |
|||
The degree to which a paramagnetic contrast agent can enhance the proton transverse relaxation rate constant (R2, 1/T2), normalized to the concentration of the contrast agent. Also referred to as r2. Typically expressed in units l/mmol/s. |
|||
Indicates normalized dose of Imaging Agent per kg of patient weight. Typically recommended by the vendor. |
|||
Information about list of administration steps for administering Imaging Agent. |
|||
A limit set at the power injector device indicating the maximum allowed pressure planned for administering the Imaging Agent. |
|||
Time after the start of injection of a delivered Imaging Agent administration. |
|||
An individual administration step in the Imaging Agent administration plan. |
|||
Time difference between the nominal start of the administration step and the actual start of Imaging Agent administration. |
|||
Time delay for start of image acquisition after start of Imaging Agent administration. |
|||
Information about a delivery phase of an Imaging Agent administration step. |
|||
The volume of the Imaging Agent in an Imaging Agent container before administration. |
|||
The volume of the Imaging Agent remaining in the Imaging Agent container after administration. |
|||
Time for the injector to build up from zero to the set pressure. |
|||
Flow rate at the start of an administration of the Imaging Agent. |
|||
Flow rate at the end of an administration of the Imaging Agent. |
|||
A vendor-specific code indicating the shape of the flow rate curve within an administration phase. |
|||
The status of the Imaging Agent administration procedure at completion as reported by the automated injector or by the administering person. |
|||
Information about adverse events occurring during administration of an Imaging Agent. |
|||
The estimated volume lost at the injection site. The estimation includes extravasation, paravenous administration and leakage at the injection site. |
|||
Date and Time when an adverse event was noticed by the observer. |
|||
The unique identifier of the Imaging Agent administration step being referenced. |
|||
The identifier of an Imaging Agent administration phase being referenced. |
|||
An injector device that can be configured to execute a series of phases automatically. |
|||
Number of injector heads or pumps (single, dual or many) in an injector device. |
|||
The volume of Imaging Agent in one unit of presentation. The capacity of the unit of presentation may be larger than this. |
|||
Information about the Imaging Agent accessory or consumable used for performing the Imaging Agent administration. |
|||
Type of consumable used for performing the Imaging Agent administration. |
|||
If the consumable is installed newly during the preparation process for this Imaging Agent Administration. |
|||
Information about the Imaging Agent administration steps that is patient-specific. |
|||
Information about the Imaging Agent administration steps that were delivered to a patient. |
|||
The maximum volume of contrast agent allowed to be administered. This is typically specified by the prescribing health care professional for patient safety and quality purposes. |
|||
Graph depicting the measurement of flow rate of fluid against time. |
|||
Graph depicting the measurement of pressure of fluid against time. |
|||
Information about two-dimensional graph data for a syringe or pump. |
|||
Information about events that occurred at an injector during an Imaging Agent administration. |
|||
Type of event that occurred at an injector during an Imaging Agent administration. |
|||
Reference to a Planned Imaging Agent Administration SOP instance. |
|||
Information about the activity in an Imaging Agent administration phase. In an Automated Injection system this describes the activity of one of the pump or syringe units used. |
|||
Volume of one agent component in a mixture of multiple components. |
|||
Total volume administered by all syringes/pump actions during a single phase. |
|||
Total volume administered by all syringes/pump actions within all phases during a single Step. |
|||
Total number of times that an injection was triggered manually. |
|||
Peak flow rate value detected at a specific location (syringe or pump) during a specific activity of an administration phase. |
|||
Peak pressure value detected at a location (syringe or pump) during a single administration phase activity. |
|||
Unique identification of a single performed Imaging Agent administration step actually delivered on a specific occasion |
|||
An injection of an inactive agent to test for blockages or leakages in the delivery path, usually performed prior to an administration of an imaging or therapeutic agent. |
|||
An injection of a bolus of Imaging Agent to determine the appropriate delay time for a diagnostic administration. |
|||
Administration of an Imaging Agent for the purpose of enhancing contrast in an image. |
|||
Type of step in an Imaging Agent administration. For example, a test administration or a diagnostic administration. |
|||
Injection of an inactive fluid to clear the administration path of an active agent. |
|||
A curve that decays exponentially from a specified start value, at a specified decay rate. |
|||
A curve that changes linearly from a specified start value to a specified end value. |
|||
Identifies an Imaging Agent uniquely within a set of Imaging Agents. The Imaging Agent may be a single component or a mix of multiple components. |
|||
A pharmaceutical agent administered as a pre-medication to prevent contrast reactions. |
|||
Unique identification of a single Imaging Agent administration performed phase. |
|||
The unique identifier of the Imaging Agent administration performed phase being referenced |
|||
A non time-determined administration phase that is not automatically terminated, where fluid delivery is stopped until manually resumed. |
|||
The Imaging Agent Administration Injector Phase Identifier used for presenting this Phase to the User Interface of the injector. Not necessarily the same as the Imaging Agent Administration Phase Identifier of the IAASR Plan. |
|||
Indicator for marking this phase as a Automated Administration Phase, which has undergone a manual hold during execution. |
|||
A programmed administration phase initiated an injector hold/wait state. |
|||
A manual intervention of the technologist initiated an injector hold/wait state. |
|||
A manual intervention of the technologist has resumed injector fluid administration. It does not matter if the hold/wait state was initiated programmed or manually. |
|||
The injector terminated injection processing from hold/wait after exceeding a time limit. |
|||
Structure of skin of inferior posterior surface of the pinna. |
|||
Structure of skin of superior posterior surface of the pinna. |
|||
A functional condition present during acquisition, such as phonation, weight bearing, voiding of the bladder or hemodynamic physiological challenges. |
|||
A circular, aperture size adjustable beam limiting device for an RT treatment device. |
|||
Physical RT external beam compensator to compensate for inhomogeneity. |
|||
RT Treatment irradiating the body of the Patient in part or in whole. |
|||
RT Treatment irradiating the surface of the skin of the Patient in part or in whole. |
|||
Patient SupportContinuous Pitch Angle at the isocenter position about the x-axis of the Equipment Coordinate System. |
|||
Patient Support Continuous Roll Angle at the isocenter position about the y-axis of the Equipment Coordinate System. |
|||
Patient Support Continuous Yaw Angle at the isocenter position about the z-axis of the Equipment Coordinate System. |
|||
Patient Support Lateral Position along the x-axis of the Equipment Coordinate System. |
|||
Patient Support Longitudinal Position along the y-axis of the Equipment Coordinate System. |
|||
Patient Support Vertical Position along the z-axis of the Equipment Coordinate System. |
|||
A type of device (or cone) for electron treatments that attaches to the applicator carriage of an RT treatment device for the purpose of holding an aperture and a bolus close to the patient's skin. Several beam applicators may be available to reduce the weight of apertures lifted by therapists, decrease the aperture/bolus-to-skin distance, and reduce leakage radiation. |
|||
A type of device (or cone) for photon treatments that is attached to the radiation head of an RT treatment device into which beam modifiers are installed. |
|||
A type of device which is used to delimit the radiation of an RT treatment device in case of an intraoperative radiotherapeutic treatment. |
|||
A physical device placed inside the radiation head used to modify the fluence distribution across the field. |
|||
A physical device manually placed between the radiation head and the patient used to modify the fluence distribution across the field. It is motorized and can be inserted/extracted from the beam path. |
|||
An effective wedge generated by the movement of a jaw across the treatment field while delivering radiation. |
|||
Mechanical grid to embed scaling information in a radiographic image |
|||
Mechanical crosshair to embed a crosshair representing axes and scaling information in a radiographic image |
|||
Beam that uses a filter to produce a nearly uniform intensity profile. |
|||
Beam that does not use a filter to produce a nearly uniform intensity profile. |
|||
Beam that uses a filter to produce a nearly uniform region across part of the intensity profile. |
|||
A medical professional capable of developing a radiotherapy plan from a Physicians prescription and assisting in radiation machine calibration and other radiotherapy quality assurance work under supervision of a Medical Physicist. |
|||
The point location defined as the nominal source of radiation. |
|||
The center point of the treatment machine through which all beam central axes pass under all gantry angles. |
|||
A fixed point at which initial patient setup is performed based on lasers. |
|||
Set of Robotic Nodes that can be used for targets associated with the patient's head. |
|||
Set of Robotic Nodes that can be used for targets within the patient's body, excluding the head. |
|||
Set of Robotic Nodes that can be used for targets near the patient's trigeminal nerve. |
|||
Two Robotic Nodes for Quality Assurance, for example daily checks. |
|||
DICOM objects communicated in time-synchronized flows using DICOM-RTV, intended for a simultaneous presentation. |
|||
Audio and Video DICOM objects communicated in time-synchronized flows using DICOM-RTV, intended for a simultaneous presentation. |
|||
Two Video DICOM objects communicated in time-synchronized flows using DICOM-RTV, intended for a stereo video. |
|||
Audio and two Video DICOM objects communicated in time-synchronized flows using DICOM-RTV, intended for a stereo video. |
|||
The purpose of defining a region. E.g., to define a bounding box, center or outline. |
|||
A visual explanation of how an algorithm produced its results. E.g., for a machine learning application, a class activation or saliency map. |
|||
Values are derived using global average pooling in convolutional neural networks to produce a localization map highlighting the important regions in the image for predicting a class. The class activation map (CAM) indicates the discriminative image regions used by the network to identify a class. |
Zhou B, Khosla A, Lapedriza A, Oliva A, Torralba A. Learning Deep Features for Discriminative Localization. IEEE Conference on Computer Vision and Pattern Recognition (CVPR). 2016. p 2921–9. http://dx.doi.org/10.1109/CVPR.2016.319 |
||
Values are derived using the gradients of a target class flowing into the final convolutional layer of a convolutional neural network to produce a localization map highlighting the important regions in the image for predicting a class. The gradient-weighted class activation map (Grad-CAM) indicates the discriminative image regions used by the network to identify a class. |
Selvaraju RR, Cogswell M, Das A, Vedantam R, Parikh D, Batra D. Grad-CAM: Visual Explanations from Deep Networks via Gradient-based Localization. 2016. http://arxiv.org/abs/1610.02391 |
||
Values are derived using a single back-propagation pass through a network to produce a localization map highlighting the spatial support of a given class in a given image. |
Simonyan K, Vedaldi A, Zisserman A. Deep Inside Convolutional Networks: Visualising Image Classification Models and Saliency Maps. 2013. http://arxiv.org/abs/1312.6034 |
||
An object which is attached to the patient to attenuate the therapeutic dose (such as a Bolus or a lead shield). |
|||
A leiomyosarcoma (sarcoma containing large spindle cells of smooth muscle) occuring at a site other than the uterus. |
|||
A measure of weighted attenuation shifts within perivascular adipose tissue, computed as a weighted measure of attenuation in concentric layers of perivascular tissue around the arterial wall, capturing the respective perivascular attenuation gradients. Abbreviated "FAI". See Antoniades C, Kotanidis CP, Berman DS. State-of-the-art review article. Atherosclerosis affecting fat: What can we learn by imaging perivascular adipose tissue? Journal of Cardiovascular Computed Tomography. 2019 Mar 29;0(0). Available from: http://www.journalofcardiovascularct.com/article/S1934-5925(18)30618-X/abstract. |
|||
A channel monitoring the patient’s rotation around the body’s longitudinal (head – feet) axis. |
|||
A channel monitoring the angle of elevation of the patient against horizontal. |
|||
Airflow measurement by a nasal piezoelectric polyvinylidenefluoride sensor. |
|||
Airflow measurement by a Continuous Positive Airway Pressure device. |
|||
Pressure delivered by a positive airway pressure device like a CPAP or BiPAP machine. |
|||
Pressure of air leaking from a positive airway pressure device like a CPAP or BiPAP machine. |
|||
Tidal volume during breathing when subject is using a positive airway pressure device like a CPAP or BiPAP machine. |
|||
Respiratory pressure measured with an unspecified method or device. |
|||
Respiratory effort delivered by a respiratory inductance plethysmography (RIP) belt applied on the patient’s thorax. |
|||
Respiratory effort delivered by a respiratory inductance plethysmography (RIP) belt applied on the patient’s abdomen. |
|||
Respiratory effort delivered by a piezoelectric polyvinylidenefluoride sensor belt applied on the patient’s thorax. |
|||
Respiratory effort delivered by a piezoelectric polyvinylidenefluoride sensor belt applied on the patient’s abdomen. |
|||
Respiratory effort measured by an unspecified method or device on the patient’s thorax. |
|||
Respiratory effort measured by an unspecified method or device on the patients abdomen. |
|||
Respiratory effort measured by an unspecified method or device. |
|||
Partial pressure of carbon dioxide in the respiratory gases measured transcutaneously. |
|||
Partial pressure of carbon dioxide measured in the end-tidal main-stream respiratory gases. |
|||
Partial pressure of carbon dioxide measured in the end-tidal main-stream respiratory gases averaged over time. |
|||
Partial pressure of carbon dioxide measured in the end-tidal side-stream respiratory gases. |
|||
Partial pressure of carbon dioxide measured in the end-tidal side-stream respiratory gases averaged over time. |
|||
Partial pressure of carbon dioxide measured in the main-stream respiratory gases. |
|||
Partial pressure of carbon dioxide measured in the side-stream respiratory gases. |
|||
Partial pressure of carbon dioxide measured in the main-stream respiratory gases averaged over time. |
|||
Partial pressure of carbon dioxide measured in the side-stream respiratory gases averaged over time. |
|||
Partial pressure of carbon dioxide in the respiratory gases measured using an unspecified method or device. |
|||
Radiotherapy treatment delivery where treatment parameters are defined at the treatment device, rather than specified by a treatment plan. |
|||
The order in which Imaging Agent administration steps are planned to be performed. |
|||
Decision was made by the operator of the equipment to discontinue treatment. |
|||
Decision was made by the physician to discontinue treatment. |
|||
An out-of-tolerance delivery parameter was accepted or re-specified and treatment delivery was continued. |
|||
The patient was re-positioned and treatment delivery was continued. |
|||
The patient could not be positioned on the patient positioning device in a way, that the shape of treatment area has an unacceptable orientation to match the intended target area. |
|||
The patient could not be positioned on the patient positioning device in a way, that the that the shape of treatment area radiated the intended target area. |
|||
The machine intended to be used for treatment was not available. |
|||
The patient´s anatomy is found to be inconsistent with the patient model used during planning to the extent that treatment delivery was impacted. |
|||
A re-calibration of the treatment device impacted the treatment delivery. |
|||
A planned Beam Modifier was not available at the time of treatment. |
|||
A capability of the treatment device was not available because the corresponding license expired. |
|||
Beam targeting parameters have been adjusted in a way that violated a clinical tolerance. |
|||
A Meterset value has been adjusted in a way that violated a clinical tolerance. |
|||
A Delivery Rate has been adjusted in a way that violated a clinical tolerance. |
|||
One or more MLC leave positions exceeded the machine tolerance. |
|||
An interlock triggered by the primary fluence-monitoring system. |
|||
An interlock triggered by the secondary fluence-monitoring system (also known as Secondary Dose Monitoring System [IEC 60601-2-1]). |
|||
Information about non-melanoma skin cancers in blood relatives of the patient. |
|||
Information about in situ melanoma in blood relatives of the patient. |
|||
The number of malignant melanomas the patient has had diagnosed. |
|||
The number of in situ melanomas the patient has had diagnosed. |
|||
Number of first-degree relatives affected by malignant melanoma |
The number of direct relatives (i.e., parent, sibling, offspring) who have malignant melanoma. |
||
A continuous part of space, not necessarily associated with a particular image. |
|||
A reference to an identifier of a Region of Interest. For example, the value of ROI Number (3006,0022) within an Item of Structure Set ROI Sequence (3006,0020) in an Instance of RT Structure Set Storage SOP Class. |
|||
A path along the long axis of an elongated finding or feature, which is equidistant from its surface, such as along the center of the lumen of a vessel. |
|||
Mode of stimulation used when applying stimulation techniques during procedure. |
|||
The sample number where the first stimulation event takes place. |
|||
The time offset where the stimulation starts, relative to the start time of the recorded waveform data. |
|||
Description of dosimetric-related values that can be summarized for the entire scope of accumulation. |
|||
Description of dosimetric-related values that can be summarized for a single irradiation event. |
|||
Description of the reference point definition and accumulated dose values at the reference point. |
|||
This acquisition of data (e.g., for constructing an image) was for some reason unsatisfactory. |
|||
The reason that data (e.g., for constructing an image) was rejected. |
|||
Description of the radiation dose characteristics independent of an irradiation event. |
|||
The component that is used to define the origin of the RDSR RCS. |
|||
The description of the RDSR reference coordinate system. It should include a description of where the origin is, as well as the orientation of the coordinate system. |
|||
Describes if a reported value is a mean, median, maximum, minimum, etc. |
|||
Description of the output measurement point dose accumulation timing and values. |
|||
The air kerma (in mGy) accumulated at the output measurement point during a given period of time. |
|||
Description of the radiation field area and corresponding timing and source index. |
|||
A list of three-dimensional coordinates that describe the perimeter of the radiation field. The points shall be coplanar and are limited to describing either polygons or ellipses. |
|||
Specifies when a value was determined within a period of time. |
|||
Description of the X-Ray source coordinate reference system and the transformation matrix that relates it to the RDSR reference coordinate system |
|||
A transformation matrix that relates one coordinate system to another |
|||
A point defining a vector relative to the center of rotation that defines a normal vector of the rotation plane |
|||
The angle about the center of rotation for a rotating object |
|||
Description of component positions described in the X-Ray source reference coordinate system |
|||
The three-dimensional coordinate of the output measurement position. The output measurement position is described in the X-Ray source reference coordinate system. |
|||
The three-dimensional coordinate of the reference point position. The reference point position is described in the X-Ray source reference coordinate system. The reference point may be at the same position as the output measurement point. |
|||
Textual identification for each attenuator described. The identifier is used to link the description of the attenuator to its position described in the beam position or attenuator position template. The identifier shall not change during the scope of accumulation described in 10040, and shall not be repeated. |
|||
Description of positions and corresponding timing for attenuators |
|||
Description of various patient attenuation characteristics that may be known by the system and may change during the course of the scope of accumulation |
|||
Description of various procedure characteristics that may change during a study and may be useful to aid in dosimetry or quality assurance |
|||
Characteristics of an X-Ray attenuator used as either a filter or attenuating object in the X-Ray beam. Includes a description of actual or equivalent material, as well as thickness information. |
|||
The point in time at the beginning of a defined period of time |
|||
The origin of the Frame of Reference is defined as part of the room in which the equipment is located |
|||
The origin of the Frame of Reference is defined as part of the equipment |
|||
The origin of the Frame of Reference is defined as part of the patient support |
|||
The origin of the Frame of Reference is defined as the isocenter of the imaging system |
|||
The origin of the RDSR Frame of Reference is defined as the origin of the patient coordinate system in the images. |
|||
A dosimetry phantom consisting of a 100 mm diameter polymethyl methacrylate (PMMA) cylinder. The phantom will be at least 140 mm in length. The phantom will be longer than the length of the sensitive volume of the radiation detector used for measurements. The phantom will have five holes just large enough to accept a radiation detector and will be parallel to the axis of symmetry: one hole at the center, and four holes with their centers 10 mm below the surface of the phantom at 90° intervals. For the holes not used during a measurement, properly fitting insert parts made of PMMA will be used. |
|||
Indication of whether endorectal coil was used during MR examination. |
|||
Substance used to fill endorectal coil in order to suppress distortion artifacts during MR examination. |
|||
Time between acquisition of imaging samples corresponding to the same tissue location during dynamic contrast-enhanced examination. |
|||
Clinical history of the patient related to the genitourinary health. |
|||
Assessment of the imaging study related to its quality, as defined by the compliance with the technical acquisition requirements or as perceived by the reader. |
|||
Assessment of a specific imaging series related to its quality, as defined by the compliance with the technical acquisition requirements or as perceived by the reader. |
|||
Standard or guideline used to perform structured evaluation of imaging study. |
|||
Information relevant for evaluation of prostate MR imaging study. |
|||
Finding relating to the overall assessment of the prostate gland |
|||
Finding relating to the localized entities within the prostate gland |
|||
Measurements relating localized findings to the prostate gland |
|||
Length of the portion of the lesion abutting the prostate capsule as observed in the image. |
|||
Finding identified in prostate MRI that is located outside of the prostate gland. |
|||
Evaluation of a localized abnormality within the gland using Prostate Imaging Reporting and Data System (PI-RADS®) guidelines. |
|||
Assessment of the lesions characteristics based on its appearance in T2-weighted MR images following the Prostate Imaging Reporting and Data System (PI-RADS®) guidelines. |
|||
Assessment of the lesions characteristics based on its appearance in diffusion-weighted MR images following the Prostate Imaging Reporting and Data System (PI-RADS®) guidelines. |
|||
Assessment of the lesions characteristics based on its appearance in Dynamic Contrast-enhanced MR images following the Prostate Imaging Reporting and Data System (PI-RADS®) guidelines. |
|||
Prostate Imaging Reporting and Data System (PI-RADS®) version 2.0. [PI-RADS]. |
|||
Prostate Imaging Reporting and Data System (PI-RADS®) version 2.1 [PI-RADS v2.1]. |
|||
Image from a diffusion-weighted acquisition corresponding to the highest b-value. |
|||
Image acquisition that involves injection of a contrast agent into the bloodstream. |
|||
Image obtained as a difference in image intensities between two phases of a dynamic contrast-enhanced acquisition. |
|||
Area of focal dilatation that occurs within the prostatic utricle. |
|||
Based on image appearance, the coil was not placed correctly. |
|||
The imaging procedure performed did not correspond to what was re |