A calorimetric detector (1) for measuring energy of electrons and photons comprises a light energy absorber and scintillating fibers (2). The absorber is formed of a tungsten matrix (3), comprising a first assembly (4) and a second assembly (5) of parallel tungsten plates. The first assembly (4) is perpendicular to the second assembly (5) forming a grid, while each plate is in one half formed by alternating teeth (6) and gaps (7). The first assembly's (4) plates fit detachably with their teeth (6) into the gaps (7) of the second assembly (5) and vice versa. Spaces between the plates of the first assembly (4) and the second assembly (5) form longitudinal sections (8) with inner cross-section size of one pixel. The scintillating fibers (2) are longitudinally arranged, made of a single crystal material. The tungsten matrix (3) is in a protective metal frame (9) having tungsten inner walls (10).

A radiation detector including: a substrate formed with a plural pixels in pixel region of a flexible base member, the plural pixels accumulates charges generated in response to light converted from radiation; a conversion layer provided at a surface to which the pixel region is provided on the base member, the conversion layer converts the radiation into light; and a reinforcement substrate provided at a surface of the conversion layer that faces a surface of the substrate side, the reinforcement substrate contains a material having a yield point and has a higher rigidity than the base member.

A whole body PET and CT combined detector and device, comprising a CT scanner frame (4) and a PET detection chamber (5) at the front and the rear along a common central axis. The CT scanner frame (4) is provided with a housing and also has a cylindrical CT scanning channel vertical to the central axis; the PET detection chamber (5) is formed by a plurality of PET detection modules (6, 7) adjacent to each other, and PET detection crystals (10) are all arranged in a direction towards to the chamber, the PET detection chamber (5) is entirely closed or a first opening is formed at the side adjacent to the CT scanner frame (4); each of the PET detection modules (6, 7) is composed of the PET detection crystals (10), a photoelectric sensor array (8), and a light guide (9); and except for the first opening, the cross-sectional areas of all gaps of the PET detection chamber (5) are smaller than the detected surface area of the smallest one of the PET detection crystals (10).

Lutetium oxide-based scintillator materials, as well as corresponding methods and systems, are described.

A scintillator panel includes a substrate made of an organic material, a barrier layer formed on the substrate and including thallium iodide as a main component, and a scintillator layer formed on the barrier layer and including cesium iodide as a main component.

According to this scintillator panel, moisture resistance can be improved by providing the barrier layer between the substrate and the scintillator layer.

An apparatus for detecting a locating medium in tissue includes a probe, and a console. The probe includes a handle and a detector disposed on a distal end of the probe. The console is in communication and includes a display. The display has a first graphical representation and a second graphical representation. The first graphical representation is configured to depict a count real-time count based on a signal from the detector. The second graphical representation is configured to depict a target count.

Inorganic perovskites doped with oxygen atoms or fluorine atoms, methods for making the doped perovskites, and hard radiation detectors incorporating the doped perovskites as photoactive layers are provided. The doped perovskites utilize lead oxide, lead fluoride, or compounds that thermally decompose into lead oxide or lead fluoride as dopant atom sources. During the crystallization of a perovskite in the presence of the dopant atom sources, oxygen or fluoride atoms from the dopant source are incorporated into the perovskite crystal lattice.

A ceramic scintillator according to the present embodiment has a composition represented by (Lu.sub.1-xPr.sub.x) .sub.a (Al.sub.1-yGa.sub.y) .sub.bO.sub.12, wherein x, y, a, and b in the composition respectively satisfy 0.005≤x≤0.025, 0.3≤y≤0.7, 2.8≤a≤3.1, and 4.8≤b≤5.2.

A rare earth halide scintillation material the chemical formula of the material being CeBr.sub.3+x, wherein 0.0001x0.1. The rare earth halide scintillation material has excellent scintillation properties including high light output, high energy resolution, and fast decay.

Codoped lutetium-based oxyorthosilicate scintillators (e.g., lutetium oxyorthosilicase (LSO) and lutetium-ytrrium oxyorthosilicate (LYSO) scintillators) codoped with transition metal ions (e.g., Cu.sup.2+) are described. The codoping can alter one or more optical and/or scintillation property of the scintillator material. For example, the codoping can increase scintillation light yield and/or decrease scintillation decay time. Radiation detectors comprising the scintillators, methods of detecting high energy radiation using the radiation detectors, and methods of altering one or more scintillation and/or optical properties of a lutetium-based oxyorthosilicate scintillator are also described.