Provided is a radiation detector that converts an intensity of received radiation into an electrical signal and a case that houses the radiation detector. An area of the case other than a predetermined area is formed of a material having durability against a disinfectant solution that has a higher disinfection effect than ethanol.

A radiation detector, such as for a PET scanner, may include an array of scintillator crystals, with each scintillator crystal having a polished end, a roughened end opposite the polished end, and polished sides extending between the polished end and the roughened end. The detector may also include a specular reflector layer between adjacent polished sides of adjacent ones of the array of scintillator crystals, and a diffusive reflector layer adjacent the roughened ends of the array of scintillator crystals. The detector may further include at least one photodetector adjacent the polished ends of the array of scintillator crystals.

A radiation detector, such as for a PET scanner, may include an array of scintillator crystals, with each scintillator crystal having a polished end, a roughened end opposite the polished end, and polished sides extending between the polished end and the roughened end. The detector may also include a specular reflector layer between adjacent polished sides of adjacent ones of the array of scintillator crystals, and a diffusive reflector layer adjacent the roughened ends of the array of scintillator crystals. The detector may further include at least one photodetector adjacent the polished ends of the array of scintillator crystals.

Provided is 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 PET scanner includes gamma-ray detector rings that form a bore through which an imaging subject is translated, a length of the bore defining an axial length of the PET scanner, the gamma-ray detector rings being movable along the axial length, the gamma-ray detector rings including gamma-ray detector modules therein, and processing circuitry configured to receive PET data associated with a plurality of transaxial slices of the imaging subject, the PET data including a first set of spatial information and timing information corresponding to a first data acquisition period for the gamma-ray detector modules in a first axial position and a second set of spatial information and timing information corresponding to a second data acquisition period for the gamma-ray detector modules in a second axial position, and reconstruct a PET image based on the first set of spatial and timing information and the second set of spatial and timing information.

A system and method for the measurement of radiation emitted from the body, for example, is presented. In one example, radiation sensors (e.g., gamma radiation sensors) may be used to measure activity proximate an injection site as a function of time. With that data, a function describing an amount of radioactive material in tissue proximate the injection site as a function of time may be estimated where an amount of radioactive material in the tissue at a time t is known. When an array of sensors is employed, the amount of radioactive material in the tissue proximate the injection site may be determined directly by the system. With an estimated function of radioactive material proximate the injection site as a function of time known, an estimated arterial input function may be determined, allowing for calculation of a correction factor that may be applied by a clinician during nuclear medical imaging.

A Proton Computed Tomography (pCT) system utilizing proton beams for construction of 3-dimensional density maps of both test phantoms and living tissue. PCT is a much sought-after modality for treatment planning and validation at proton therapy treatment centers, as it would allow in situ imaging with the same beam that is used for the treatment. A pCT system according to the present invention includes gaseous detectors for tracking and energy reconstruction, a shutter system to extend dynamic range features while maintaining good energy resolution, and a method for determining proton energy from a forward-search algorithm utilizing segmentation of energy detector ionization signal readout. The gaseous detectors are Gas Electron Multiplier (GEM) based gaseous detectors.

Provided is 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.