Abstract: An ionizing radiation detector module (22) includes a detector array (200), a memory (202), signal processing electronics (208), a communications interface (210), and a connector (212). The memory contains detector performance parameters (204) and detector correction algorithms (206). The signal processing electronics (208) uses the detector performance parameters (204) to correct signals from the detector array (200) in accordance with the detector correction algorithms (206).

Abstract: A computed tomography method includes rotating an electron beam along an anode (104) disposed about an examination region (112) for a plurality of sampling intervals in which x-ray projections are sampled. The electron beam is swept during each sampling interval to generate a plurality of successive focal spots at different focal spot locations during each sampling interval, wherein the focal spots generated in a given sampling interval include a sub-set of the focal spots generated in a previous sampling interval. The x-ray projections radiated from each of the plurality of focal spots is sampled during each sampling interval. The resulting data is reconstructed to generate volumetric image data.

Abstract: A diagnostic imaging system includes a stationary gantry (20) which defines a subject-receiving bore (26). First and second lasers (66, 68) are firmly mounted to the stationary gantry (20). A saggital laser (48) is mounted overhead to project a longitudinal line (58) on a top of the subject in a vertical plane (60) which is parallel to an axial direction (Z). A couch (36) moves a subject into the bore (26)to generate an image of a region of interest and out of the bore for marking. A user segments the image to outline at least an organ. An isocenter (94) of the segmented organ is determined. At least one of the saggital, first and second lasers (48, 66, 68) are adjusted concurrently with adjusting the couch (36) such that laser lines (58, 76, 78) projected by the saggital, first and second lasers (48, 66, 68) intersect the determined isocenter (94). The saggital, first and second lasers (48, 66, 68) laser mark the subject.

Abstract: A radiographic imaging apparatus (10) comprises a primary radiation source (14) which projects a beam of radiation into an examination region (16). A detector (18) converts detected radiation passing through the examination region (16) into electrical detector signals representative of the detected radiation. The detector (18) has at least one temporally changing characteristic such as an offset B(t) or gain A(t). A grid pulse means (64) turns the primary radiation source (14) ON and OFF at a rate between 1000 and 5000 pulses per second, such that at least the offset B(t) is re-measured between 1000 and 5000 times per second and corrected a plurality of times during generation of the detector signals. The gain A(t) is measured by pulsing a second pulsed source (86, 100, 138) of a constant intensity (XRef) with a second pulse means (88). The gain A(t) is re-measured and corrected a plurality of times per second during generation of the detector signals.

Abstract: A radiation detector module (22) particularly well suited for use in computed tomography (CT) applications includes a scintillator (200), a photodetector array (202), and signal processing electronics (205). The photodetector array (202) includes a semiconductor substrate (208) having a plurality of photodetectors and metalization (210) fabricated on non-illuminated side of the substrate (208). The metalization routes electrical signals between the photodetectors and the signal processing electronics (205) and between the signal processing electronics (205) and an electrical connector (209).

Abstract: A diagnostic imaging system (10) includes an x-ray source (16), which is rotated around an examination region (20) on a rotating gantry (14). A subject, disposed on a couch (30), is translated longitudinally through the examination region (20). The imaging system is standardized such that a common subassembly is adapted to receive a bore (24) of any selectable diameter. The common subassembly includes a stationary gantry (12) and a bearing race (52) supported by bearing members (50). Standard motor modules (28), standard power slip ring modules (56), and standard information transmission modules (58) are disposed about the race (52). The number of the standard modules (28, 56, 58) is specified by a user.

Abstract: An ionizing radiation detector module (22) includes a detector array (200), a memory (202), signal processing electronics (208), a communications interface (210), and a connector (212). The memory contains detector performance parameters (204) and detector correction algorithms (206). The signal processing electronics (208) uses the detector performance parameters (204) to correct signals from the detector array (200) in accordance with the detector correction algorithms (206).

Abstract: A radiation detector module includes a scintillator (62, 62?, 162, 262) arranged to receive penetrating radiation of a computed tomography apparatus (10). The scintillator produces optical radiation responsive to the penetrating radiation. A detector array (66, 66?, 166, 266) is arranged to convert the optical radiation into electric signals. Electronics (72, 72?, 172, 272) are arranged on a side of the detector array opposite from the scintillator in a path of the penetrating radiation. A radiation shield (86, 86?, 100, 100?, 100?, 186, 210, 210?, 286, 286?) is disposed between the detector array and the electronics to absorb the penetrating radiation that passes through the scintillator. The radiation shield includes openings (90, 90?) that communicate between the detector array and the electronics. Electrical feedthroughs (88, 88?, 102, 102?, 102?, 188, 212, 212?, 288, 288?) pass through the radiation shield openings and electrically connect the detector array and the electronics.

Abstract: A diagnostic imaging system (10) includes an x-ray source (16), which is rotated around an examination region (20) on a rotating gantry (14). A subject, disposed on a couch (30), is translated longitudinally through the examination region (20). The imaging system is standardized such that a common subassembly is adapted to receive a bore (24) of any selectable diameter. The common subassembly includes a stationary gantry (12) and a bearing race (52) supported by bearing members (50). Standard motor modules (28), standard power slip ring modules (56), and standard information transmission modules (58) are disposed about the race (52). The number of the standard modules (28, 56, 58) is specified by a user.

Abstract: A radiation detector module includes a scintillator (62, 62?, 162, 262) arranged to receive penetrating radiation of a computed tomography apparatus (10). The scintillator produces optical radiation responsive to the penetrating radiation. A detector array (66, 66?, 166, 266) is arranged to convert the optical radiation into electric signals. Electronics (72, 72?, 172, 272) are arranged on a side of the detector array opposite from the scintillator in a path of the penetrating radiation. A radiation shield (86, 86?, 100, 100?, 100?, 186, 210, 210?, 286, 286?) is disposed between the detector array and the electronics to absorb the penetrating radiation that passes through the scintillator. The radiation shield includes openings (90, 90?) that communicate between the detector array and the electronics. Electrical feedthroughs (88, 88?, 102, 102?, 102?, 188, 212, 212?, 288, 288?) pass through the radiation shield openings and electrically connect the detector array and the electronics.

Abstract: A data measurement system (DMS) (30) for a computed tomography (CT) scanner (12) includes a plurality of connectorized detector sub-array modules (32). Each detector sub-array module (32) includes: a scintillator (40) that produces scintillation events responsive to irradiation by x-rays; a photodetector array (42) arranged to detect the scintillations; and two symmetrically arranged signal connectors (541, 542) that transmit the photodetector signals. Symmetrically mounted pipeline cards (60) mate with the signal connectors (54) of each side of groups of the detector sub-array modules (32) to receive the photodetector signals. A processor (64) communicating with the pipeline cards (60) receives the photodetector signals from the pipeline cards (60) and constructs a DMS output from the photodetector signals.

Abstract: A data measurement system (DMS) (30) for a computed tomography (CT) scanner (12) includes a plurality of connectorized detector sub-array modules (32). Each detector sub-array module (32) includes: a scintillator (40) that produces scintillation events responsive to irradiation by x-rays; a photodetector array (42) arranged to detect the scintillations; and two symmetrically arranged signal connectors (541, 542) that transmit the photodetector signals. Symmetrically mounted pipeline cards (60) mate with the signal connectors (54) of each side of groups of the detector sub-array modules (32) to receive the photodetector signals. A processor (64) communicating with the pipeline cards (60) receives the photodetector signals from the pipeline cards (60) and constructs a DMS output from the photodetector signals.

Abstract: A computerized tomographic imaging system including a stationary gantry portion defining an examination region and a rotating gantry portion for rotation about the examination region. An x-ray source is disposed on the rotating gantry portion for projecting x-rays through the examination region. A plurality of modular radiation detector units are disposed across the examination region from the x-ray source. Each radiation detector unit includes an array of x-ray sensitive cells for receiving radiation from the x-ray source after it has passed through the examination region and for generating an analog signal indicative of the radiation received thereby. Each radiation detector unit also includes a plurality of integrated circuits connected to the x-ray sensitive cells with each integrated circuit including a plurality of channels. Each channel receives the analog signal from an x-ray sensitive cell and generates digital data indicative of the value of the analog signal.

Abstract: A CT scanner (10) includes a reconstruction processor (32) and a mosaic X-Radiation detector (20). The mosaic detector includes plural detector elements (22, 22, 23, 24, 25, 26) arranged in abutting relationship and configured for the desired imaging application. The detector elements include scintillating crystals (50) in optical communication with a back-illuminated photodiode array (52) or modified top-surface photodiode array (152, 252) for converting emitted light into electrical charge. The photodiode array is mounted on a carrier substrate (58) via bump (56) bonding. The carrier substrate provides a conductive path routing the photodiode array output through to contacts on the back side for connection to readout electronics (60). The carrier substrate and readout electronics are contained within the footprint defined by the photodiode array, allowing the detector elements to be abutted on any and all sides, thus permitting the mosaic detector to be tailored to any desired size and shape.

Abstract: A computerized tomographic imaging system including a stationary gantry portion defining an examination region and a rotating gantry portion for rotation about the examination region. An x-ray source is disposed on the rotating gantry portion for projecting x-rays through the examination region. A plurality of modular radiation detector units are disposed across the examination region from the x-ray source. Each radiation detector unit includes an array of x-ray sensitive cells for receiving radiation from the x-ray source after it has passed through the examination region and for generating an analog signal indicative of the radiation received thereby. Each radiation detector unit also includes a plurality of integrated circuits connected to the x-ray sensitive cells with each integrated circuit including a plurality of channels. Each channel receives the analog signal from an x-ray sensitive cell and generates digital data indicative of the value of the analog signal.