A radiation imaging system includes a radiation imaging apparatus and an imaging control apparatus, the radiation imaging apparatus includes a dose detection pixel that detects a dose of radiation irradiated from a radiation source, and the imaging control apparatus controls the radiation imaging apparatus. Before radiation imaging, the imaging control apparatus specifies a position of the dose detection pixel in a region of interest for calculating a dose indicator value of a radiation image, determines a threshold according to the position of the dose detection pixel, and transmits the position of the dose detection pixel and the threshold to the radiation imaging apparatus. The radiation imaging apparatus makes a setting of the position of the dose detection pixel in the region of interest and the threshold transmitted from the imaging control apparatus, and performs imaging based on the setting.

In one aspect, a radiation detector is disclosed, which includes a substrate having a plurality of microcapillary channels, and a crystalline scintillator material disposed in said channels so as to generate a plurality of independent radiation sensing elements associated with each channel for detecting incident radiation and generating an optical radiation in response to the detection of the incident radiation. In some embodiments, the incident radiation can include any of alpha (α), beta (β), gamma (γ), X-ray and neutrons.

A diagnostic imaging system utilizing a reduced crystal design pattern is utilized to image a subject and collect event data. The reduced crystal design pattern includes filled crystal locations and empty crystal locations. A processor accounts for empty crystal locations by selecting windows that include nearest neighbor filled crystal locations. The nearest neighbor filled crystal locations include event data which is averaged by the processor and assigned to the empty crystal location. A weighted average based on distance or event strength is incorporated.

A channel multiplexing method for reading array detector signals includes: dividing array detectors into M groups, at least two detectors being in each group; array coding the read channel to read M row signals and N column signals, which means when a signal is outputted at the detector in row a, column b, the signals of row a and column b are outputted correspondingly; connecting the readout signals of-the row and the column to different positions of two transmission lines respectively; determining the source row number and column number of the signal on the basis of the time difference between the time of signal reaching two ends of the transmission line, and marking the source detector from which the signal is generated on the basis of two time differences of the row signal and the column signal.

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.

In beta emission imaging, magnetic lensing allows a lower resolution detector to detect the spatial distribution of emissions at a higher resolution. The sample is placed in a magnetic field with field lines at a given density, and the detector is placed away from the sample where the magnet field lines diverge, resulting in a lesser density. Since the beta emissions travel along the field lines, the divergence of the field lines from the sample to the detector result in lensing or magnification. Using positron attenuation tomography to detect annihilation in the detector allows for correction due to self-absorption by the sample. The correction and lensing are used together or may be used independently.

A sensor network, which includes a sensor controller serially coupled to a plurality of sensor modules, is configured to program the sensor modules so as to transfer measurement data to the sensor controller and to synchronize the sensor modules to picosecond accuracy via on-chip or on-module custom circuits and a physical layer protocol. The sensor network has applications for use in PET, LiDAR or FLIM applications. Synchronization, within picosecond accuracy, is achieved through use of a picosecond time digitization circuit. Specifically, the picosecond time digitization circuit is used to measure on-chip delays with high accuracy and precision. The delay measurements are directly comparable between separate chips even with voltage and temperature variations between chips.

The disclosure relates to a system and method for medical imaging. The method may include: move, by a motion controller, a phantom along an axis of a scanner to a plurality of phantom positions; acquire, by a scanner of the imaging device, a first set of PET data relating to the phantom at the plurality of phantom positions; and store the first set of PET data as an electrical file. The length of an axis of the phantom may be shorter than the length of an axis of the scanner, and at least one of the plurality of phantom positions may be inside a bore of the scanner.

A method and apparatuses for a radiation detector apparatus, comprising a scintillator array comprising a plurality of scintillator crystals. The plurality of scintillator crystals includes a first scintillator crystal and a second scintillator crystal adjacent to the first scintillator crystal within the scintillator array. A photosensor array comprising a plurality of photosensors including a first photosensor configured to detect photons from the first scintillator crystal. A first separator positioned between the first scintillator crystal and the second scintillator crystal. First separator optically separates the first scintillator crystal and the second scintillator crystal such that the first photosensor detects photons from the first scintillator crystal and not from the second scintillator crystal.

Disclosed herein are variations of megavoltage (MV) detectors that may be used for acquiring high resolution dynamic images and dose measurements in patients. One variation of a MV detector comprises a scintillating optical fiber plate, a photodiode array configured to receive light data from the optical fibers, and readout electronics. In some variations, the scintillating optical fiber plate comprises one or more fibers that are focused to the radiation source. The diameters of the fibers may be smaller than the pixels of the photodiode array. In some variations, the fiber diameter is on the order of about 2 to about 100 times smaller than the width of a photodiode array pixel, e.g., about 20 times smaller. Also disclosed herein are methods of manufacturing a focused scintillating fiber optic plate.