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.

A quality assurance device for a medical accelerator includes a housing having an inner radioluminescent layer adapted to provide a visual indication when contacted with invisible radiation generated by the medical accelerator. In addition, the quality assurance device includes one or more cameras located within the housing and adapted to image the inner radioluminescent layer of the housing including the visual indication.

A quality assurance device for a medical accelerator includes a housing having an inner radioluminescent layer adapted to provide a visual indication when contacted with invisible radiation generated by the medical accelerator. In addition, the quality assurance device includes one or more passive optical components within the housing adapted to deliver an image of the inner radioluminescent layer of the housing including the visual indication to one or more cameras located outside of the housing.

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.

Detector module designs for radiographic imaging include first and second layers of scintillator rods or pixel arrays oriented in first and second directions. The first and second directions are transversely oriented to define a light sharing region between the first and second layers. Encoding features may be disposed in, on or between the first and second layers, and configured to modulate propagation of optical signals therealong or therebetween.

An imaging system is provided. A method for installing the imaging system is provided. The imaging system may include a first modality imaging apparatus. The first modality imaging apparatus may have a detector including a scintillator unit, a photodetector unit, a circuit unit, a supporting block, and a supporting board. The supporting block may be disposed on an end of the scintillator unit. The supporting board may be disposed between the photodetector unit and the circuit unit.

Detector module designs for radiographic include first and second layers of scintillator rods or pixel arrays oriented in first and second directions. The first and second directions are transversely oriented to define a light sharing region between the first and second layers. Encoding features may be disposed in, on or between the first and second layers, and configured to modulate propagation of optical signals therealong or therebetween.

A radiation position detection method includes: a first step of calculating a first centroid position in an incident direction regarding positions where scintillation light is detected, on the basis of electrical signals; and a second step of specifying, on the basis of a first table showing first identification regions for identifying the plurality of segments, and the first centroid position, the segment that initially generates the scintillation light. The first identification region includes a first region, a second region, and a third region. In the second step, in a case where the first centroid position is located in the first region or the third region, the first segment is specified as the segment that initially generates the scintillation light, and in a case where the first centroid position is located in the second region, the second segment is specified as the segment that initially generates the scintillation light.

An imaging unit includes: a first sensor module; a second sensor module; a processing substrate; a first connection member; and a second connection member. The first sensor module includes a first lens and a first sensor. The second sensor module includes a second lens and a second sensor. The processing substrate executes image processing based on the first image signal and the second image signal. The first connection member electrically connects the first sensor module and the processing substrate, and has flexibility. The second connection member electrically connects the second sensor module and the processing substrate, and has flexibility.

A radiation detector with first and second scintillator structures is disclosed. The first scintillator structure comprises a plurality of first scintillator pixels. The first scintillator pixels are separated by gaps, which may be filled with a reflective material to achieve an optical separation of the first scintillator pixels. The second scintillator structure is adapted to increase the absorption of radiation and the output of light. Thereto, the second scintillator structure overlaps at least partially the gaps between first scintillator pixels. The second scintillator structure is optically coupled to the first scintillator structure, so that light emitted by the second scintillator structure is fed into first scintillator pixels. The second scintillator structure may be mounted onto the first scintillator structure using additive manufacturing.