A radiation spectrometer includes a scintillator, a photomultiplier, and one or more light-emitting diodes (LEDs). The scintillator receives radiation from the environment and emits light that is indicative of an energy of the radiation. The photomultiplier receives the light and outputs an electrical signal that is in turn indicative of the energy of the radiation. Spectral data can be generated based upon the electrical signal, wherein the spectral data indicates a number of radiation events in each of several energy bins. The one or more LEDs can emit LED light through the scintillator and toward the photomultiplier, wherein the LED light causes an LED peak in the spectral data that can be used to identify an absolute energy of radiation events in the spectral data.

Provided are a system and method for combining detector signals. In one exemplary embodiment, the system includes the detector, a plurality of ASICs where each ASIC may receive an electric signal from the detector and generate a position signal and an energy signal based on the received electric signal, a combiner that may combine a position signal output from a first ASIC and a position signal output from a second ASIC to generate a combined position signal, and combine an energy signal output from the first ASIC and an energy signal output from the second ASIC to generate a combined energy signal, and an analog-to-digital converter that may receive the combined position signal and the combined energy signal and generate digitized image data for the first ASIC and the second ASIC based thereon.

Provided are a system and method for combining detector signals. In one exemplary embodiment, the system includes the detector, a plurality of ASICs where each ASIC may receive an electric signal from the detector and generate a position signal and an energy signal based on the received electric signal, a combiner that may combine a position signal output from a first ASIC and a position signal output from a second ASIC to generate a combined position signal, and combine an energy signal output from the first ASIC and an energy signal output from the second ASIC to generate a combined energy signal, and an analog-to-digital converter that may receive the combined position signal and the combined energy signal and generate digitized image data for the first ASIC and the second ASIC based thereon.

A radiation detector includes a sensor substrate, a conversion layer, and a neutral stress plane adjustment member. The sensor substrate includes a flexible base member, and a layer provided on a first surface of the base member and formed with plural pixels configured to accumulate electrical charge generated in response to light converted from radiation. The conversion layer is provided on the opposite side of the layer formed with the plural pixels to the side where the base member is provided and is configured to convert radiation into the light. The neutral stress plane adjustment member is provided on a second surface side of the base member on the opposite side of the base member to the first surface and is configured to adjust a position of a neutral stress plane to within a predetermined range in a stacking direction.

A radiation detector includes a sensor substrate, a conversion layer, and a neutral stress plane adjustment member. The sensor substrate includes a flexible base member, and a layer provided on a first surface of the base member and formed with plural pixels configured to accumulate electrical charge generated in response to light converted from radiation. The conversion layer is provided on the opposite side of the layer formed with the plural pixels to the side where the base member is provided and is configured to convert radiation into the light. The neutral stress plane adjustment member is provided on a second surface side of the base member on the opposite side of the base member to the first surface and is configured to adjust a position of a neutral stress plane to within a predetermined range in a stacking direction.

A radiation monitor includes a radiation detection unit detecting radiation, and an optical fiber transmitting photons emitted from a light emitting element of the radiation detection unit, wherein the radiation detection unit includes a first light emitting element generating a photon in response to incident radiation, a chemical compound part having chemical compounds which generate charged particles by nuclear reactions with incident neutrons, and a second light emitting element being located between the first light emitting element and the chemical compound part and generating a photon in response to radiation.

A radiation monitor includes a radiation detection unit detecting radiation, and an optical fiber transmitting photons emitted from a light emitting element of the radiation detection unit, wherein the radiation detection unit includes a first light emitting element generating a photon in response to incident radiation, a chemical compound part having chemical compounds which generate charged particles by nuclear reactions with incident neutrons, and a second light emitting element being located between the first light emitting element and the chemical compound part and generating a photon in response to radiation.

Provided is a PET detector for reducing the number of silicon photomultipliers in use, which is characterized in that: the detector comprises layers respectively formed by a scintillation crystal array unit and a silicon photomultiplier (4) array unit, the scintillation crystal array unit and the silicon photomultiplier (4) array unit are rectangular cross sections in plan view, and the scintillation crystal array unit and the silicon photomultiplier (4) array unit have the same area of the rectangular cross sections in plan view; the scintillation crystal array unit consists of a plurality of scintillation crystal strips (1) parallel to each other, free of gaps and attached to each other on sides, the scintillation crystal strips (1) are all cuboids with uniform length, width and height; the silicon photomultiplier (4) array unit is an array assembly, which is formed by M silicon photomultiplier (4) arrays and has the rectangular cross section in plan view.

Provided is a PET detector for reducing the number of silicon photomultipliers in use, which is characterized in that: the detector comprises layers respectively formed by a scintillation crystal array unit and a silicon photomultiplier (4) array unit, the scintillation crystal array unit and the silicon photomultiplier (4) array unit are rectangular cross sections in plan view, and the scintillation crystal array unit and the silicon photomultiplier (4) array unit have the same area of the rectangular cross sections in plan view; the scintillation crystal array unit consists of a plurality of scintillation crystal strips (1) parallel to each other, free of gaps and attached to each other on sides, the scintillation crystal strips (1) are all cuboids with uniform length, width and height; the silicon photomultiplier (4) array unit is an array assembly, which is formed by M silicon photomultiplier (4) arrays and has the rectangular cross section in plan view.

According to embodiment, an X-ray computed tomography apparatus includes an X-ray tube, an X-ray detector including a scintillator generating scintillation light upon incidence of X-ray photons and a photodetection element, a peak value detector detecting peak values corresponding to X-ray photons based on an output signal from the element, processing circuitry determining an attenuation characteristic of the light by each X-ray photon and an output decreased characteristic of the element, based on the values and time when each peak value was detected, correcting the detected values according to the characteristics, a counter counting the X-ray photons corresponding to the respective corrected peak values, wherein the processing circuitry reconstructs a medical image based on an output from the counter.