Provided is are a particle detection device and method of fabrication thereof. The particle detection device includes a scintillator array that includes a plurality of scintillator crystals; a plurality of detectors provided on a bottom end of the scintillator array; and a plurality of prismatoids provided on a top end of the scintillator array. Prismatoids of the plurality of prismatoids are configured to redirect particles between top ends of crystals of the scintillator array. Bottom ends of a first group of crystals of the scintillator array are configured to direct particles to a first detector of the plurality of detectors and bottom ends of a second group of crystals of the scintillator array are configured to direct particles to a second detector substantially adjacent to the first detector.

A method and a system for single photon emission computed tomography (SPECT) imaging capable of performing a rapid acquisition of imaging data. The SPECT imaging system, placed at a fixed radial distance from the center of an object being imaged, includes a gamma detector and a collimator. The collimator, mounted on the gamma detector, includes a plurality of parallel slats, each perpendicular to the surface of the gamma detector. The method implemented by this system rapidly reconstructs a high-resolution and high-sensitivity image.

A nuclear detector comprises a scintillation crystal array including a plurality of scintillation crystal bars of the same size arranged closely and in sequence, a light guide, and a photodetector array including a plurality of photodetectors arranged in sequence. The photodetectors have a cross-sectional area greater than that of the scintillation crystal bars, and the light guide includes a top surface coupled to the scintillation crystal array, an opposed bottom surface coupled to the photodetector array and a side surface. The light guide has a thickness in a range of 0.1 mm to 40 mm. The light guide further includes a slit adjacent to an edge of the light guide, and the slit is configured to extend from the top surface toward the bottom surface of the light guide and the slit has a depth in a range of 0.1 to 0.5 times the thickness of the light guide.

A PET imaging device for observing a brain includes a hollow three-dimensional structure with a shape capable of housing a head. The PET imaging device comprising multiple independent gamma ray detection modules that together form a structure capable of surrounding the head, said detection modules comprise continuous scintillation crystal blocks, wherein continuous means that the crystal blocks can be continuous in one or in two directions, each of the continuous scintillation crystal blocks has a polygonal main cross-section, and said structure is an elongated structure having a major axis in a direction corresponding to the front-nape direction and a shorter axis in a direction corresponding to a straight line joining ears on the head. The continuous scintillation crystal blocks are positioned adjacent to fit laterally in an exact manner with each other throughout their entire thickness, building a mosaic, without gaps between adjacent crystal blocks and without overlapping each other.

A system and method include execution of a first nuclear imaging scan to acquire first nuclear imaging scan data of a body; generation of a target image based on the first nuclear imaging scan data execute a second nuclear imaging scan to acquire second nuclear imaging scan data of the body association of each of a plurality of portions of the second nuclear imaging scan data with a respective one of a plurality of motion phases of the body, generation, for each of the plurality of motion phases of the body, of a binned image based on the portion of the second nuclear imaging scan data associated with the motion phase, performance of motion-correction on each of the plurality of binned images based on the target image to generate a plurality of motion-corrected binned images, and generation of an image based on the target image and the plurality of motion-corrected binned images.

The invention relates to a PET imaging device for observing the brain, characterised by comprising a structure with a shape that is capable of accommodating a human head, having independent gamma-ray detection modules, said detection modules having continuous scintillation crystals with a polygonal main section, wherein all together the detection modules form a hollow three-dimensional structure that can surround the head, and with said three-dimensional structure being elongated and having a main axis in the direction corresponding to the forehead-nape direction and a shorter axis in the direction corresponding to the straight line joining the ears, and with the adjacent scintillation crystals fitting together laterally in a precise manner along their entire thickness, forming a mosaic-like structure, i.e. without leaving gaps and without overlapping with one another.

A radiation therapy system is equipped with a combined imaging system, such as an imaging system combining computed tomography (CT), spectral CT, and single photon emission tomography imaging (SPECT), for guidance of radiation beams providing radiotherapy. The system can include at least one x-ray source that emits an x-ray beam at a low energy level for imaging and/or an x-ray beam at a high energy level for radiation therapy. The system can also include at least one imager, such as a cadmium zinc telluride (CZT) or cadmium telluride (CdTe) flat-panel imager that receives x-ray beams traversing a subject from the x-ray source and gamma rays emitted by radioisotope tracers injected into the subject. Based on the guidance of the triple images (CT, spectral CT, and SPECT), a computer system can control the radiation therapeutic beam delivery to target areas, such as lesions and/or tumors.

A radiation detector includes an array of detector pixels each including an array of detector cells. Each detector cell includes a photodiode biased in a breakdown region and digital circuitry coupled with the photodiode and configured to output a first digital value in a quiescent state and a second digital value responsive to photon detection by the photodiode. Digital triggering circuitry is configured to output a trigger signal indicative of a start of an integration time period responsive to a selected number of one or more of the detector cells transitioning from the first digital value to the second digital value. Readout digital circuitry accumulates a count of a number of transitions of detector cells of the array of detector cells from the first digital state to the second digital state over the integration time period.

Aspects of the subject disclosure may include, for example, a device comprising: a first micro-camera-element comprising a first sensor area and a first aperture element, the first aperture element having a first structural configuration, the first aperture element and the first sensor area being disposed relative to each other in order to cooperate in obtaining first imaging data having first characteristics, and the first characteristics comprising first imaging resolution and first angular coverage; a second micro-camera-element comprising a second sensor area and a second aperture element, the second aperture element having a second structural configuration, the second aperture element and the second sensor area being disposed relative to each other in order to cooperate in obtaining second imaging data having second characteristics, the second characteristics comprising second imaging resolution and second angular coverage, and the first imaging resolution differing from the second imaging resolution, the first angular coverage differing from the second angular coverage, or any combination thereof. Additional embodiments are disclosed.

Methods and systems are provided for adjusting sensitivity of detectors in a nuclear medicine imaging system based on a sensitivity table. In one embodiment, a method comprises acquiring, with a detector including a collimator, scan data of a subject administered with a radioisotope; calculating a sensitivity of the detector based on the collimator and the radioisotope; and calculating a quantitative parameter from the acquired scan data of the subject based on the calculated sensitivity. In this way, SPECT quantitation may be accurately performed due to the increased accuracy of detector sensitivity for a given collimator and radioisotope without specifically calibrating the detector for the given collimator and radioisotope.