The present specification provides a detector for an X-ray imaging system. The detector includes at least one high resolution layer having high resolution wavelength-shifting optical fibers, each fiber occupying a distinct region of the detector, at least one low resolution layer with low resolution regions, and a single segmented multi-channel photo-multiplier tube for coupling signals obtained from the high resolution fibers and the low resolution regions.

A combined scintillation crystal includes: at least one scintillation crystal A module and a scintillation crystal B module. The scintillation crystal A module and the scintillation crystal B module are scintillation crystal modules with different performances. The scintillation crystal A module comprises at least one scintillation crystal A, and the scintillation crystal B module comprises at least one scintillation crystal B. The sensitivity of the scintillation crystal A is lower than the sensitivity of the scintillation crystal B, and the light output ability of the scintillation crystal A is higher than the light output ability of the scintillation crystal B. The scintillation crystal B module includes a ray incidence plane for receiving rays, and the at least one scintillation crystal module A is arranged at the outer side of the ray incidence plane of the scintillation crystal B module.

The present specification provides a detector for an X-ray imaging system. The detector includes at least one high resolution layer having high resolution wavelength-shifting optical fibers, each fiber occupying a distinct region of the detector, at least one low resolution layer with low resolution regions, and a single segmented multi-channel photo-multiplier tube for coupling signals obtained from the high resolution fibers and the low resolution regions.

A radiation imaging apparatus comprising a first scintillator, a second scintillator which receives radiation transmitted through the first scintillator, conversion elements and a controller is provided. The conversion elements include first conversion elements and second conversion elements with different sensitivities for detecting light emitted from at least one of the first scintillator or the second scintillator. During radiation irradiation, the controller obtains, from a signal output from one or more measuring element configured to measure a dose of incident radiation, a first signal corresponding to light converted from radiation by the second scintillator, and outputs, based on the first signal, a stop signal configured to stop the radiation irradiation, and after the radiation irradiation, the controller causes the first conversion elements and the second conversion elements to output signals configured to generate an energy subtraction image.

Various techniques are provided to detect the direction and location of one or more radiation sources. In one example, a system includes a plurality of radiation detectors configured to receive radiation from a radiation source. A first one of the radiation detectors is positioned to at least partially occlude a second one of the radiation detectors to attenuate the radiation received by the second radiation detector. The system also includes a processor configured to receive detection information provided by the first and second radiation detectors in response to the radiation, and determine a direction of the radiation source using the detection information. A modular system including gamma radiation detectors and neutron radiation detectors and related methods are also provided. In some cases, radiation source type may be determined in addition to or separate from radiation source direction.

A ray detector substrate has detection regions and includes a substrate, a first interdigital electrode and a second interdigital electrode disposed on a side of the substrate and located in each detection region, a first scintillator layer disposed on a side of the first interdigital electrode and the second interdigital electrode away from the substrate, and a second scintillator layer disposed on a side of first scintillator layer away from the substrate. The second scintillator layer is configured to convert part of rays incident onto the detection region into visible light, and transmit another part of the rays, so that the another part of the rays is incident onto the first scintillator layer through the second scintillator layer. The first scintillator layer is configured to convert the visible light converted by the second scintillator layer and the another part of the rays through the second scintillator layer into photocurrent.

The present invention relates to an X-ray detector (10) comprising two or more scintillator layers, comprising: a first scintillator layer (20); a second scintillator layer (30); a first photodiode array (40); a second photodiode array (50); and at least one light emitting layer (60). The first scintillator layer is configured to absorb X-rays from an X-ray pulse and emit light. The first photodiode array is positioned adjacent to the first scintillators layer. The first photodiode array is configured to detect at least some of the light emitted by the first scintillator layer. The second scintillator layer is configured to absorb X-rays from the X-ray pulse and emit light. The second photodiode array is positioned adjacent to the second scintillator layer. The second photodiode array is configured to detect at least some of the light emitted by the second scintillator layer. The at least one light emitting layer is 10 configured to emit radiation such that at least some of the emitted radiation irradiates the first photodiode array and at least some of the emitted radiation irradiates the second photodiode array.

An X-ray detector comprises a first scintillator layer, a second scintillator layer, a first photodiode array, a second photodiode array, and at least one light emitting layer. The first scintillator layer is configured to absorb X-rays from an X-ray pulse and emit light. The first photodiode array is positioned adjacent to the first scintillator layer and is configured to detect at least some of the light emitted by the first scintillator layer. The second scintillator layer is configured to absorb X-rays from the X-ray pulse and emit light. The second photodiode array is positioned adjacent to the second scintillator layer and is configured to detect at least some of the light emitted by the second scintillator layer. The at least one light emitting layer is configured to emit radiation such that at least some of the emitted radiation irradiates the first photodiode array, and at least some of the emitted radiation irradiates the second photodiode array.

A ray detector substrate includes: photodetectors including first photodetectors and second photodetectors; and dimming portions including, at a side of each first photodetector away from a substrate, a respective first dimming portion, and, at a side of each second photodetector away from the substrate, a respective second dimming portion. A second scintillator layer is configured to convert part of rays into a first radiation fluorescence. A first scintillator layer is configured to convert another part of the rays into a second radiation fluorescence. The first dimming portion is configured to reflect the second radiation fluorescence, and to enable the first radiation fluorescence to pass through the first dimming portion to be detected by the first photodetector. The second dimming portion is configured to reflect the first radiation fluorescence, and to enable the second radiation fluorescence to pass through the second dimming portion to be detected by the second photodetector.

A device for the detection of gamma rays used primarily in a PET scanner is based on a scintillator heterostructure combining the high stopping power of scintillators commonly used in PET scanners (such as L(Y)SO, BGO, etc.) and very fast scintillators based on polymers loaded with fast emitting dyes or nanocrystals, or thin layers of nanocrystals or multiple quantum well structures. The particular arrangement of this detector module allows combining all the important features of a high-performance Time-of-Flight PET (TOFPET) detector module, i.e., a high photoelectric detection efficiency for the gamma rays, a precise 3D information (including the depth of interaction DOI) of the gamma ray conversion in the module, and good energy resolution.