Abstract: A radiation detector includes an array of detector pixels each including an array of detector cells. Each detector cell includes a photodiode biased in a breakdown region and digital circuitry coupled with the photodiode and configured to output a first digital value in a quiescent state and a second digital value responsive to photon detection by the photodiode. Digital triggering circuitry is configured to output a trigger signal indicative of a start of an integration time period responsive to a selected number of one or more of the detector cells transitioning from the first digital value to the second digital value. Readout digital circuitry accumulates a count of a number of transitions of detector cells of the array of detector cells from the first digital state to the second digital state over the integration time period.

Abstract: A data processing device, comprising a plurality of emitter antennas arranged on a movable data acquisition device and adapted to emit electromagnetic radiation including data acquired by the movable data acquisition device, a plurality of receiver antennas each adapted to receive the electromagnetic radiation emitted by each of the plurality of emitter antennas, and a data processing unit coupled to the plurality of receiver antennas and adapted to extract the data acquired by the movable data acquisition device from the electromagnetic radiation received by the plurality of receiver antennas.

Abstract: A family of photodetectors includes at least first and second members. In one embodiment, the family includes members having different pixel sizes. In another, the family includes members having the same pixel size. The detection efficiency of the detectors is optimized to provide a desired energy resolution at one or more energies of interest.

Abstract: A photodetector array (142) includes a plurality of photodetector cells (202) such as avalanche photodiodes (208) and readout circuits (210). An array self-tester (226) tests a dark count or other performance characteristic of the cells (202). The test is performed in connection with the manufacture of the array (142) or following the installation of the array (142) in a detection system (100).

Abstract: A radiation detector (46) includes a semiconductor layer(s) (12) formed on a substrate (14) and a scintillator (30) formed on the semiconductor layer(s) (12). The semiconductor layer(s) (12) includes an n-doped region (16) disposed adjacent to the substrate (14), and a p-doped region (18) disposed adjacent to the n-doped region (16). A trench (20) is formed within the semiconductor layer(s) (12) and around the p-doped region (18) and is filled with a material (22) that reduces pn junction curvature at the edges of the pn junction, which reduces breakdown at the edges. The scintillator (30) is disposed over and optically coupled to the p-doped regions (18). The radiation detector (46) further includes at least one conductive electrode (24) that electrically contacts the n-doped region.

Abstract: A detector arrangement providing imaging information at the edge of the scintillator is provided. The detector arrangement provides complete information and improved spatial resolution. SiPMs can be used in place of PMTs in order to provide the geometrical coverage of the scintillator and improved spatial resolution. With such detector arrangements, the spatial resolution can be under 2 mm. Furthermore, the overall thickness of the detector can be substantially reduced and depth of interaction resolution is also improved.

Abstract: An imaging system (2) having a scalable event processing architecture includes a plurality of detector modules (4) arranged around an associated imaging region (8) to detect radiation events emitted from a subject disposed within the imaging region (8); a plurality of sets of processing elements (6), each set including processing elements of at least one of the plurality of radiation detector modules (4), each processing element (6) time-stamping an associated detected radiation events; and inserting the time-stamped event into a chronological position within a data stream (10) of events; and coincident detecting circuitry (22, 54) that receives the chronologically ordered stream of events and detects coincident pairs of events for use in reconstructing one or more associated images of the object.

Abstract: A photodiode includes an anode (1202, 1302, 1402) and a cathode (1306, 1406) formed on a semiconductor substrate (402). A vertical electrode (702, 1314, 1414) is in operative electrical communication with a buried component (502, 1312, 1412) of the photodiode. In one implementation, the photodiode is an avalanche photodiode of a silicon photomultiplier. The substrate may also include integrated CMOS readout circuitry (1102).

Abstract: A radiation detector includes an array of detector pixels each including an array of detector cells. Each detector cell includes a photodiode biased in a breakdown region and digital circuitry coupled with the photodiode and configured to output a first digital value in a quiescent state and a second digital value responsive to photon detection by the photodiode. Digital triggering circuitry is configured to output a trigger signal indicative of a start of an integration time period responsive to a selected number of one or more of the detector cells tranisitioning from the first digital value to the second digital value. Readout digital circuitry accumulates a count of a number of transitions of detector cells of the array of detector cells from the first digital state to the second digital state over the integration time period.

Abstract: In a combined scanner, a main magnet (20) and magnetic field gradient coils (28) housed in or on a scanner housing (12, 18) acquires spatially encoded magnetic resonances in an imaging region (14). Solid state radiation detectors (50, 50?, 50?) disposed in or on the scanner housing are arranged to detect gamma rays emitted from the imaging region. Time-of-flight positron emission tomography (TOF-PET) processing (52, 54, 58, 60, 62) determines localized lines of response based on (i) locations of substantially simultaneous gamma ray detections output by the radiation detectors and (ii) a time interval between said substantially simultaneous gamma ray detections. TOF-PET reconstruction processing (64) reconstructs the localized lines of response to produce a TOF-PET image. Magnetic resonance imaging (MRI) reconstruction processing (44) reconstructs the acquired magnetic resonances to produce an MRI image.

Abstract: A positron emission tomography apparatus (100) includes a plurality of radiation sensitive detector systems (106) and selective trigger systems (120). The selective trigger systems identify detector signals resulting from detected gamma radiation (310) while disregarding spurious detector signals (310). In one implementation, the apparatus (100) includes a time to digital converter which decomposes a measurement time interval (Tmax) according to a binary hierarchical decomposition of level H, where H is an integer greater than equal to one.

Abstract: An imaging system (2) having a scalable event processing architecture includes a plurality of detector modules (4) arranged around an associated imaging region (8) to detect radiation events emitted from a subject disposed within the imaging region (8); a plurality of sets of processing elements (6), each set including processing elements of at least one of the plurality of radiation detector modules (4), each processing element (6) time-stamping an associated detected radiation events; and inserting the time-stamped event into a chronological position within a data stream (10) of events; and coincident detecting circuitry (22, 54) that receives the chronologically ordered stream of events and detects coincident pairs of events for use in reconstructing one or more associated images of the object.

Abstract: A radiation detector (46) includes a semiconductor layer(s) (12) formed on a substrate (14) and a scintillator (30) formed on the semiconductor layer(s) (12). The semiconductor layer(s) (12) includes an n?doped region (16) disposed adjacent to the substrate (14), and a p?doped region (18) disposed adjacent to the n?doped region (16). A trench (20) is formed within the semiconductor layer(s) (12) and around the p?doped region (18) and is filled with a material (22) that reduces pn junction curvature at the edges of the pn junction, which reduces breakdown at the edges. The scintillator (30) is disposed over and optically coupled to the p?doped regions (18). The radiation detector (46) further includes at least one conductive electrode (24) that electrically contacts the n?doped region.

Abstract: In a combined scanner, a main magnet (20) and magnetic field gradient coils (28) housed in or on a scanner housing (12, 18) acquires spatially encoded magnetic resonances in an imaging region (14). Solid state radiation detectors (50, 50?, 50?) disposed in or on the scanner housing are arranged to detect gamma rays emitted from the imaging region. Time-of-flight positron emission tomography (TOF-PET) processing (52, 54, 58, 60, 62) determines localized lines of response based on (i) locations of substantially simultaneous gamma ray detections output by the radiation detectors and (ii) a time interval between said substantially simultaneous gamma ray detections. TOF-PET reconstruction processing (64) reconstructs the localized lines of response to produce a TOF-PET image. Magnetic resonance imaging (MRI) reconstruction processing (44) reconstructs the acquired magnetic resonances to produce an MRI image.

Abstract: A data processing device, comprising a plurality of emitter antennas (140) arranged on a movable data acquisition device and adapted to emit electromagnetic radiation including data acquired by the movable data acquisition device, a plurality of receiver antennas (150) each adapted to receive the electromagnetic radiation emitted by each of the plurality of emitter antennas (140), and a data processing unit (118) coupled to the plurality of receiver antennas (150) and adapted to extract the data acquired by the movable data acquisition device from the electromagnetic radiation received by the plurality of receiver antennas (150).

Abstract: A radiation detector includes an array of detector pixels each including an array of detector cells. Each detector cell includes a photodiode biased in a breakdown region and digital circuitry coupled with the photodiode and configured to output a first digital value in a quiescent state and a second digital value responsive to photon detection by the photodiode. Digital triggering circuitry is configured to output a trigger signal indicative of a start of an integration time period responsive to a selected number of one or more of the detector cells tranisitioning from the first digital value to the second digital value. Readout digital circuitry accumulates a count of a number of transitions of detector cells of the array of detector cells from the first digital state to the second digital state over the integration time period.