A product includes a transparent scintillator material, a beta emitter material having an end-point energy of greater than 225 kiloelectron volts (keV), and a photovoltaic portion configured to convert light emitted by the scintillator material to electricity. A thickness the scintillator material is sufficient to protect the photovoltaic portion from significant radiation damage.

A PET detector having some light guides not cut, comprising a light guide bar array unit having some light guides not cut. The light guide bar array unit is in the form of an array consisting of a plurality of parallel light guide bars (2), and adjacent light guide bars (2) in some regions of the light guide bar array unit and a reflective material (4) between every two light guide bars are replaced with a light guide three-dimensional block having the identical shape and volume, taken as a whole. The detector sequentially comprises a layer formed by a scintillating crystal array unit, a layer formed by the light guide bar array unit, and a layer formed by a silicon photomultiplier array unit in an arrangement order.

The disclosure relates to a scintillation pixel array, a radiation sensing apparatus, a scintillation apparatus, and methods of making a scintillation pixel array wherein scintillation pixels have beveled surfaces and a reflective material around the beveled surfaces. The embodiments described herein can reduce the amount of cross-talk between adjacent scintillation pixels.

The radiation detector (10) comprises a scintillator (15) having a first refractive index (n.sub.s) for converting incident radiation (RR) received at a first side (S1) of the radiation detector (10) into converted radiation (CR), a photosensor (20) for receiving the converted radiation (CR) from the scintillator (15), and an optical coating layer (25) arranged between the scintillator (15) and the photosensor (20). The scintillator (15) has regions (RR) arranged for being imaged, when impinged by the incident radiation (RR), onto corresponding regions of the photosensor (20). The optical coating layer (25) has a second refractive index (n.sub.o) lower than the first refractive index (n.sub.s) for reflecting the converted radiation (CR) resulting from the incident radiation (RR) impinged on a particular region (A1) of the scintillator (15) and received by a region (A3) of the optical coating layer (25) corresponding to a photosensor region different from the imaged one (A2).

A detector assembly for a CT imaging system is provided. The detector assembly including a scintillator block including a plurality of pixels, each pixel configured to receive x-ray beams travelling in a transmission direction, a plurality of photodiodes, and a light guide coupled between the scintillator block and the plurality of photodiodes, the light guide including a plurality of light pipes, each light pipe configured to guide light emitted from a pixel of the plurality of pixels into an associated photodiode of the plurality of photodiodes, wherein each pixel has a first cross-sectional area that is substantially perpendicular to the transmission direction, wherein each photodiode has a second cross-sectional area that is substantially perpendicular to the transmission direction, and wherein the first cross-sectional area is different from the second cross-sectional area.

Single X-ray grating differential phase contrast (DPC) X-ray imaging is provided by replacing the conventional X-ray source with a photo-emitter X-ray source array (PeXSA), and by replacing the conventional X-ray detector with a photonic-channeled X-ray detector array (PcXDA). These substitutions allow for the elimination of the G0 and G2 amplitude X-ray gratings used in conventional DPC X-ray imaging. Equivalent spatial patterns are formed optically in the PeXSA and the PcXDA. The result is DPC imaging that only has a single X-ray grating (i.e., the G1 X-ray phase grating).

The present invention provides a scintillator panel which is provided with a narrow barrier rib with high accuracy in a large area, has a high light emission luminance, and provides sharp images. The present invention provides a scintillator panel including: a plate-like substrate; a grid-like barrier rib provided on the substrate; and a scintillator layer containing a phosphor filled in cells divided by the barrier rib, wherein the barrier rib is mainly composed of a low-melting-point glass, and the substrate is formed of a material which is mainly composed of a ceramic selected from the group consisting of alumina, aluminum nitride, mullite and steatite.

A radiation detection apparatus may include a scintillator to emit scintillating light in response to absorbing radiation, a photosensor to generate an electronic pulse in response to receiving the scintillating light, and a reflector surrounding the photosensor. The photosensor may be coupled to a wiring board and the reflector may be coupled to the wiring board. The radiation detection apparatus can be more compact and more rugged as compared to radiation detection apparatuses that include a photomultiplier tube.

A curved radiographic detector has electromagnetic radiation sensitive elements disposed in a two-dimensional array. A curved housing encloses the two-dimensional array of radiation sensitive elements and includes a layer of aligned carbon nanotubes on a surface thereof.

The invention concerns a scintillation detector with which high count rates and/or high resolutions are possible. The scintillator of the claimed scintillation detector is formed from pixels (2), which are separated from each other by interstices (4). Alternatively or additionally, the surface of the scintillator is divided by grooves into pixels (2). Such a structure enables not only a particularly high resolution. When multiple detector modules are used, it also allows high count rates in the range of roughly 20 MHz.