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.

A method for electro-depositing a radioactive material onto a metal substrate is disclosed. This is particularly well-suited for true random number generators. The method includes (a) at least partially masking the metal substrate to expose a metallic surface on the metal substrate; (b) connecting the metal substrate to a cathode of a current source; (c) submersing the exposed metallic surface into a solution containing radioactive metal ions, wherein the solution is connected to an anode of the current source; (d) removing the exposed metallic surface from the solution; (e) removing the solution from the exposed metallic surface; (f) measuring the amount of radioactivity emitted from the exposed metallic surface; and (g) repeating steps (c) through (f) until the amount of radioactivity measured in step (f) stabilizes relative to a previous measurement.

According to one embodiment, a radiation detector includes first and second resin members, a detection part, a wiring part, and a controller. The first resin member includes first and second partial regions, and a third partial region between the first and second partial regions. The second resin member includes fourth and fifth partial regions. The detection part is provided between the first and fourth partial regions. The detection part includes a first conductive layer, a second conductive layer provided between the first conductive layer and the fourth partial region, and an organic semiconductor layer provided between the first and second conductive layers. The wiring part is provided between the third and fifth partial regions. The wiring part includes first and second wiring layers. The controller is fixed to the second partial region. The controller is electrically connected with the first and second wiring layers.

According to one embodiment, a radiation detector includes first and second resin members, a detection part, a wiring part, and a controller. The first resin member includes first and second partial regions, and a third partial region between the first and second partial regions. The second resin member includes fourth and fifth partial regions. The detection part is provided between the first and fourth partial regions. The detection part includes a first conductive layer, a second conductive layer provided between the first conductive layer and the fourth partial region, and an organic semiconductor layer provided between the first and second conductive layers. The wiring part is provided between the third and fifth partial regions. The wiring part includes first and second wiring layers. The controller is fixed to the second partial region. The controller is electrically connected with the first and second wiring layers.

Disclosed are a ray converter and a ray detection panel device. The ray converter (100, 100′) includes a substrate (110) and a conversion body (120). The substrate (110) includes a medium carrier. The medium carrier has a mesoporous structure distributed in an array. A pore of the mesoporous structure extends from an entrance end of the substrate (110) to an exit end of the substrate (110). The conversion body (120) is filled in the pore. The ray detection panel device includes a ray converter (100, 100′) and a light sensor.

A photoelectric conversion panel includes a TFT, a photodiode disposed at an upper layer than the TFT, a first organic film formed at an upper layer than the photodiode, a first inorganic insulating film covering at least a part of the first organic film, and a second organic film covering at least a part of the first inorganic insulating film. The first inorganic insulating film includes a first hole portion connecting the first organic film and the second organic film, and a first moisture-proof portion at least a part of which is disposed at a side of the photodiode with respect to the first hole portion. The first moisture-proof portion penetrates the first organic film.

A portable computed tomography (CT) system includes an O-shaped gantry defining an opening, an x-ray source operably coupled to the O-shaped gantry, and a flat panel detector (FPD) coupled to the O-shaped gantry and having a two-dimensional anti-scatter grid (2D ASG) coupled to a side of the FPD facing the opening. With the O-shaped gantry having the FPD, the object may be imaged in a first field of view (FOV) with the detector arranged in a centered geometry. Then, the detector may be arranged in an offset geometry, through-holes of the ASG may be aligned with x-ray emission paths of the x-ray source, and the object may be imaged in a second FOV with the detector arranged in the offset geometry.

A system and method for imaging by gamma radiation detection having at least one processing unit analyzing at least one signal provided by at least one set of detection modules mounted on a frame and including, on the one hand, at least one module of Compton camera type having a field of view directed towards a volume delimited by the frame and, on the other hand, at least one pair of coincidence detection PET modules, diametrically opposite to each other on the frame and defining an imaging axis, the processing unit analyzing the signal derived from the Compton-type module to determine the intersection of the imaging axis with the field of view and to determine the optimal orientations and/or locations of the various detection modules on the frame so that the imaging axis passes through the source of the gamma radiation in the object to be imaged.

A scintillator structure includes a plurality of cells and a reflector covering the plurality of cells. Here, each of the plurality of cells includes a resin and a phosphor, and the phosphor contains gadolinium oxysulfide. A breaking strength of an interface between each of the plurality of cells and the reflector is 900 gf or more.