The disclosure relates to a system and method for evaluating and calibrating detector in a scanner, further evaluating and calibrating time information detected by at least one time-to-digital convertor.

A radiation imaging apparatus including: a first scintillator layer configured to convert a radiation (R) which has entered the first scintillator layer into light; a second scintillator layer configured to convert a radiation transmitted through the first scintillator layer into light; a fiber optic plate (FOP) provided between the first scintillator layer and the second scintillator layer; and an imaging portion configured to convert the light generated in the first scintillator layer and the light generated in the second scintillator layer into an electric signal.

An imaging system generates a first radiograph based on a first pattern of radiation detected by a Linear Diode Array (LDA) radiation detector positioned to detect a radiation beam emitted by a radiation generator. The LDA radiation detector comprises a plurality of modules. Each respective module of the plurality of modules comprises a respective plurality of photodiodes corresponding to pixels. Furthermore, the imaging system may determine, based on the first radiograph, a size of a gap between two of the modules of the LDA radiation detector. After determining the size of the gap, the imaging system may generate a second radiograph based on a second pattern of radiation detected by the LDA radiation detector. The imaging system may generate a third radiograph by modifying, based on the size of the gap, the second radiograph to compensate for the gap.

A radiation diagnostic device according to an aspect of the present invention includes a first detector, a second detector, and processing circuitry. The first detector detects Cherenkov light that is generated when radiation passes. The second detector is disposed to be opposed to the first detector on a side distant from a generation source of the radiation, and detects energy information of the radiation. The processing circuitry specifies Compton scattering events detected by the second detector, and determines an event corresponding to an incident channel among the specified Compton scattering events based on a detection result obtained by the first detector.

An X-ray detector includes a detection unit to convert X-rays into a signal value and an evaluation unit. The detection unit and the evaluation unit are configured in a common component, the extent of the component along a first direction being not greater than the extent of the detection unit. The evaluation unit includes at least one correction unit to correct the signal values, a computation unit to control the correction, and a memory unit to store at least one correction parameter. The evaluation unit is designed such that the signal values are corrected as a function of the at least one correction parameter. A method and detector group are also disclosed.

An apparatus for detecting X-rays and converting the detected X-ray intensities into digital signals is disclosed. The apparatus places Analog to Digital Conversion (ADC) chips directly under a scintillator array along the X-ray beam direction and uses a shield that is placed between a photodiode substrate and an Analog to Digital Conversion (ADC) chip to block X-rays from directly reaching the dies of the ADC chips, which are sensitive to X-rays. Also an X-ray CT system utilizing the disclosed apparatus for detecting X-rays is provided.

There is provided a detector component (40) for an X-ray or gamma ray detector, the detector component (40) comprising: a scintillating crystal having a plurality of scintillation crystal pixels (41), wherein each scintillating crystal pixel (41) is larger in one dimension than in the other two dimensions, and wherein each scintillating crystal pixel (41) has one or more light exit faces; and a photodetector (42) associated with at least one of the light exit faces of each scintillating crystal pixel (41), wherein a first and a second scintillating crystal pixel are arranged adjacent to one another, wherein a X-ray or gamma ray interaction with the first scintillating crystal pixel causes the generation of at least one photon, and optical cross talk of the at least one generated photon occurs between the first and the second scintillating crystal pixel, such that the X-ray or gamma ray interaction within the first scintillating crystal pixel is detected in use at the photodetector associated with a light exit face of the second scintillating crystal pixel.

A radiation imaging apparatus that is able to perform radiography using a grid in which a radiation transmissive layer and a radiation absorption layer each having a strip shape and extending in a first direction are alternately arranged in a second direction, the radiation imaging apparatus includes a pixel unit including a plurality of imaging pixels and a plurality of detection pixels, wherein the plurality of detection pixels includes a first detection pixel and a second detection pixel that are in a pair in the second direction, an output signal value of the first detection pixel is larger than an average value of output signal values of the plurality of imaging pixels and the plurality of detection pixels, and an output signal value of the second detection pixel is smaller than the average value.

A radiation detector has reflection materials that segment a scintillator array to respective areas, a first accumulator 41, which adds multiple signals amplified by amplifiers 30 in the area segmented by the reflection materials, per area segmented by the reflection materials, a first trigger generation circuit 42, that generates a trigger of the signals added by the first accumulator, per area segmented by the reflection materials. When the signals are added, the superimposition of the inherent noises of each amplifier 30 can be reduced as much as the area segmented by the reflection materials, so that the signal noise can be reduced by increasing the S/N (signal/noise) ratio. The signals (timing signals) are respectively and separately generated based on each trigger in the different area to each other and converged by the encoder 50, so that probability of pileup (multiple pileups) can be reduced and an accurate timing signal can be obtained.

Among other things, a detector unit for a detector array of a radiation imaging modality is provided. In some embodiments, the detector unit comprises a radiation detection sub-assembly and an electronics sub-assembly. The electronics sub-assembly comprises electronic circuitry, embedded within a molding compound, configured to digitize analog signals yielded from the radiation detection sub-assembly and/or to otherwise process such analog signals. The electronics sub-assembly also comprises a substrate, such as a printed circuit board, configured to route signals between the electronic circuitry and a photodetector array of the radiation detection sub-assembly and/or to route signals between the electronic circuitry and digital processing components, such as an image generator, for example.