A device for generating one or more images of a source distribution of a gamma radiation field in the near and far field can include a detector system that includes several synchronized detectors for detecting radiation, system electronics that registers coincidence events, a data acquisition system that stores the measurement data of the coincidence events, and an analysis unit that performs an image reconstruction, which reconstructs one or more images of the source distribution of the radiation field.

A scintillation detector, including a scintillator that emits scintillation; a semiconductor photodetector having a surface area for receiving the scintillation, wherein the surface area has a passivation layer configured to provide a peak quantum efficiency greater than 40% for a first component of the scintillation, and the semiconductor photodetector has built in gain through avalanche multiplication; a coating on the surface area, wherein the coating acts as a bandpass filter that transmits light within a range of wavelengths corresponding to the first component of the scintillation and suppresses transmission of light with wavelengths outside said range of wavelengths; and wherein the surface area, the passivation layer, and the coating are controlled to increase the temporal resolution of the semiconductor photodetector.

This disclosure describes an imaging radiation detection module with novel configuration of the scintillator sensor allowing for simultaneous optimization of the two key parameters: detection efficiency and spatial resolution, that typically cannot be achieved. The disclosed device is also improving response uniformity across the whole detector module, and especially in the edge regions. This is achieved by constructing the scintillation modules as hybrid structures with continuous (also referred to as monolithic) scintillator plate(s) and pixellated scintillator array(s) that are optically coupled to each other and to the photodetector. There are two basic embodiments of the novel hybrid structure: (1) the monolithic scintillator plate is at the entrance for the incoming radiation, preferably gamma rays, and the pixellated array placed behind the plate, all in optical contact with the photodetector, (2) the order of the scintillator components is reversed with the pixellated scintillation plate placed in front of the monolithic plate.

A photon detector includes a sensor array of optical sensors disposed in a plane and four substantially identical scintillation crystal bars. Each optical sensor is configured to sense luminescence. Each of the four scintillator crystal bars being a rectangular prism with four side surfaces and first and second end surfaces, each scintillation bar has two side surfaces which each face a side surface of another scintillation bar, and each scintillation crystal bar generating a light scintillation in response to interacting with a received gamma photon. A first layer (80) is disposed in a first plane disposed between and adjacent facing side surfaces of the four substantially identical scintillation crystal bars with a light sharing portion (82) adjacent the first end surface and a reflective portion (84) adjacent the second end surface. A second layer (68) is disposed in a second plane orthogonal to the first plane and disposed between and adjacent facing side surfaces of the four substantially identical scintillation crystal bars with a light sharing portion (88) adjacent the second end surface and a reflective portion (90) adjacent the first end surface.

An imaging system (36) includes a Positron Emission Tomography (PET) scanner (38) and one or more processors (52). The Positron Emission Tomography (PET) scanner (38) which generates event data including true coincident events and scatter events, the event data includes each end point of a line of response (LOR) and an energy of each end point. The one or more processors (52) are programmed to generate (72) a plurality of activity map and attenuation map pairs based on the true coincident events, and select (76) an activity map and an attenuation map from the plurality of activity and attenuation map pairs based on the scattered events.

Provided is a silicon photomultiplier (SiPM) device and a silicon photomultiplier based LiDAR. The SiPM device includes a first sub-region and a second sub-region. In the first sub-region, the photodiode is operated with a first internal gain. In the second sub-region, the photodiode is operated with a second internal gain and the second internal gain in smaller than the first internal gain. A first anode generates current from the first sub-region in response to a low flux event, and the second anode generates current from the second sub-region in response to a high flux event. A common cathode outputs current generated from the first sub-region or the second sub-region.

Provided is are a particle detection device and method of fabrication thereof. The particle detection device includes a scintillator array that includes a plurality of scintillator crystals; a plurality of detectors provided on a bottom end of the scintillator array; and a plurality of prismatoids provided on a top end of the scintillator array. Prismatoids of the plurality of prismatoids are configured to redirect particles between top ends of crystals of the scintillator array. Bottom ends of a first group of crystals of the scintillator array are configured to direct particles to a first detector of the plurality of detectors and bottom ends of a second group of crystals of the scintillator array are configured to direct particles to a second detector substantially adjacent to the first detector.

A medical diagnostic-imaging apparatus of an embodiment includes plural converters and processing circuitry. The converters output an electrical signal based on an incident radioactive ray. The processing circuitry identifies a first signal intensity that is a signal intensity corresponding to a peak of the number of the radioactive rays based on a relationship between a signal intensity of an electrical signal output from the convertor and the number of incident radioactive rays, for each of the converters. The processing circuitry identifies a second signal intensity that is a signal intensity corresponding to energy of a radioactive ray that has entered therein without scattering, based on a relationship between the signal intensity and the number of radioactive rays in a higher intensity than the first signal intensity. The processing circuitry corrects a signal intensity of an electrical signal that is output from the respective converters such that the second signal intensity identified for each of the converters matches with a target signal intensity.

Method and apparatus for scanning a region of interest (ROI) by a gamma detector. An exemplary method includes determining, for each of multiple detector configurations, a respective weight based on an absorption profile, associating each of a plurality of portions of the ROI with a respective gamma attenuation value; and detecting gamma radiation from multiple detector configurations for time periods allocated among the detector configurations based on the weights determined.

A timing apparatus and method for a radiation detection, measurement, identification and imaging system are disclosed. The apparatus comprises high-energy photon detectors (100), a light pulse signal generator (300) and an optical fiber (200). Each high-energy photon detector (100) comprises a scintillation crystal and optical-to-electrical conversion multiplying devices. The high-energy photon detectors (100) are all provided with light transmission holes. Light pulse signals are propagated to the scintillation crystals through the light transmission holes (400), then propagated to the surfaces of the optical-to-electrical conversion multiplying devices through the scintillation crystals, converted and multiplied by the optical-to-electrical conversion multiplying devices, and processed and read by an electronic circuit. The high-energy photon detectors (100) independent from each other acquire absolute time from the light pulse signals generated by the light pulse generator (300) and timing and calibration are performed between the independent high-energy photon detectors (100). Timing is achieved through the time at which the optical-to-electrical multiplication devices receive the light pulse signals, decoupling between the high-energy photon detectors (100) can be realized, the independence of the high-energy photon detectors (100) is ensured, and thus the system can use, increase or decrease the high-energy photon detectors (100) more conveniently.