The invention relates to a gamma radiation detector that provides compensation for the parallax effect. The gamma radiation detector includes a plurality of scintillator elements, a planar optical detector array, and a pinhole collimator that includes a pinhole aperture. Each scintillator element has a gamma radiation receiving face and an opposing scintillation light output face. The gamma radiation receiving face of each scintillator element faces the pinhole aperture for generating scintillation light in response to gamma radiation received from the pinhole aperture. The scintillator elements are arranged in groups. Each group has a group axis that is aligned with the pinhole aperture and is perpendicular to the radiation receiving face of each scintillator in that group. The scintillation light output faces of each of the scintillator elements are in optical communication with the planar optical detector array.

The present disclosure relates to a system for imaging. The system may include a supporting assembly and a detector assembly. The supporting assembly may include a detection region to accommodate a subject. The detector assembly may surround the detection region. The detector assembly may be configured to detect radiation rays emitted from the subject located within the detection region. The detector assembly may include a plurality of detector rings. Each detector ring may include a scintillator array and a plurality of photosensors. The plurality of detector rings may be arranged on the supporting assembly in an axial direction of the supporting assembly to form an axial field of view (FOV) having a length no less than 0.75 meters.

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.

A detector array is provided for detecting radiation photons. The detector array includes a phosphor screen that converts radiation photons into light energy. The detector array includes a photodiode array having a plurality of photodiodes that convert the light energy into electrical charge. A first photodiode of the plurality of photodiodes is spaced apart from a second photodiode of the plurality of photodiodes to define a non-detection region. The phosphor screen overlies the first photodiode, the second photodiode, and the non-detection region between the first photodiode and the second photodiode.

Detector modules, detectors and medical imaging devices are provided. One of the detector modules includes: a support and a plurality of detector sub-modules arranged on the support along an extension direction in which the support extends. Each of the detector sub-modules has a first area and a second area in the extension direction. A detecting device is disposed in the first area, and a functional module is disposed in the second area. The functional module is electrically connected to the detecting device for receiving an electrical signal from the detecting device. The plurality of detector sub-modules includes a first detector sub-module and a second detector sub-module that are arranged adjacent to each other in the extension direction, and the first area of the first detector sub-module at least partially overlaps with the second area of the second detector sub-module.

A radiation imaging apparatus including pixels each including a conversion element and a switch element, a signal line to which signals are supplied from the pixels, a readout circuit reading out a signal supplied to the signal line and a processor processing a signal read out by the readout circuit, is provided. The readout circuit performs, during irradiation with radiation, a first operation of reading out a signal while the switch element of each of the pixels is in a non-conduction state and a second operation of reading out a signal while the switch element of a predetermined pixel of the pixels is in a conduction state. The processor corrects a second signal value of a signal read out by the second operation by using a first signal value of a signal read out by the first operation.

The invention discloses a scanning method and apparatus suitable for scanning a pipeline or process vessel in which a beam of gamma radiation from a source is emitted through the vessel to be detected by an array of detectors which are each collimated to detect radiation over a narrow angle relative to the width of the emitted radiation beam.

The present disclosure relates to the use of X-ray detector cassettes that may be abutted or overlapped to form a detector assembly suitable for imaging objects that are too large to image using a single X-ray detector cassette. Such a detector assembly may be customized in terms of the size and/or shape of the field-of-view (FOV). In certain embodiments the radiation-sensitive electronics (e.g., readout electronics) are positioned to the side of the X-ray detecting components (e.g., scintillator, TFT array, and so forth), allowing the cassette to be thin relative to other detector devices and allowing the electronics to remain outside the X-ray beam path.

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 radiation detector module including a scintillator element configured to generate optical signals in response to incident radiation. A photodetector is coupled to at least a first surface of the scintillator element, the photodetector configured to convert the optical signals into output characterizing the radiation. An acoustic array is coupled to at least a second surface of the scintillator element, the acoustic array configured to convert acoustic signals generated in the scintillator element into output characterizing acoustic energy deposited therein.