A radiation detector (5) is configured such that weighting of detection signals of photodetectors (52) on an end portion side of the plurality of photodetectors (52) is set to be greater than weighting of detection signals of photodetectors (52) on a central portion side of the plurality of photodetectors (52).

A scintillator panel including a scintillator layer that converts incident radiation into light and a scintillator base that supports the scintillator layer, a sensor panel including a sensor substrate that is disposed on a side of the scintillator layer that is opposite to the scintillator base and has a photoelectric conversion portion that converts the light into an electric signal, and a sensor base that is disposed on the side of the sensor substrate that is opposite to the scintillator layer and supports the sensor substrate, and a sealing member that seals a gap between the scintillator panel and the sensor panel at an edge of the scintillator panel are comprised. The sensor panel is provided with a convex member for narrowing the gap at a position in a vertical direction to a surface of the sensor panel from the edge of the scintillator panel.

A radiation diagnostic device according to an aspect of the present invention includes a first detector, a second detector, and processing circuitry. The first detector detects Cherenkov light that is generated when radiation passes. The second detector is disposed to be opposed to the first detector on a side distant from a generation source of the radiation, and detects energy information of the radiation. The processing circuitry specifies Compton scattering events detected by the second detector, and determines an event corresponding to an incident channel among the specified Compton scattering events based on a detection result obtained by the first detector.

A nuclear medicine diagnosis apparatus according to an embodiment includes a scintillator configured to emit self-radiation, storage, and processing circuitry. The storage stores first detection efficiency correction data that is generated based on an external radiation source or a simulation and first detection efficiency data per scintillator that is calculated based on radiation that is emitted from the scintillator. The processing circuitry calculates second detection efficiency data per scintillator that is calculated based on radiation that is emitted from the scintillator and generates second detection efficiency correction data based on the first detection efficiency correction data, the first detection efficiency data, and the second detection efficiency data.

A radiographic apparatus includes a sensor panel that obtains a radiographic image by converting radiation incident thereon into an electric signal, a sensor support base that supports the sensor panel, and a housing that houses the sensor panel and the sensor support base therein. The housing includes a stack structure including a first conductor layer, a second conductor layer electrically connected to the first conductor layer via an electric connection member, and a nonconductor layer disposed between the first conductor layer and the second conductor layer.

The present invention relates to a detector arrangement for an X-ray phase contrast system (5), the detector arrangement (1) comprising: a scintillator (11); an optical grating (12); and a detector (13); wherein the optical grating (12) is arranged between the scintillator (11) and the detector (13); wherein the scintillator (11) converts X-ray radiation (2) into optical radiation (3); wherein the optical grating (12) is configured to be an analyzer grating being adapted to a phase-grating (21) of an X-ray phase contrast system (5); wherein the optical path between the optical grating (12) and the scintillator (11) is free of focusing elements for optical radiation. The present invention further relates to a method (100) for performing X-ray phase contrast imaging with a detector arrangement (1) mentioned above. The invention avoids the use of an X-ray absorption grating as G2 grating in an X-ray phase contrast interferometer system.

According to an embodiment, a photoelectric conversion element includes a photoelectric conversion layer that converts light to charges. The photoelectric conversion layer contains oligothiophene and fullerene selected from a group including a fullerene and derivatives thereof. A content ratio of the oligothiophene and the fullerene is 500:1 to 5:1 by weight.

Disclosed herein are methods of making and using an absorption-unit array suitable for X-ray detection and a detector comprising such an absorption-unit array. The methods of making the absorption-unit array may include forming the absorption-unit array on a substrate and forming a guard ring encompassing more than one absorption units of the absorption-unit array after separating the absorption-unit array from the substrate; or may include forming a plurality of absorption units and a guard ring encompassing more than one of the absorption units on a portion of a substrate after separating the portion from the substrate. The method of using an absorption-unit array may include using some of the absorption units of the absorption-unit array as a guard ring by applying an electrical voltage. A detector suitable for X-ray detection comprises an absorption layer and an electronics layer, wherein the absorption layer comprises an absorption-unit array.

An anti-scatter grid (ASG) for X-ray imaging with a surface (S) formed from a plurality of strips (LAM). The plurality of strips including at least two guard strips (L.sub.i,L.sub.i+1) that are thicker in a direction parallel to said surface than one or more strips (l.sub.i) of said plurality of strips (LAM). The one or more strips (l.sub.i) being situated in between said two guard strips (L.sub.i,L.sub.i+1).

A scintillator material includes a polymer matrix, a primary dye in the polymer matrix, the primary dye being a fluorescent dye; a secondary dye, and a Li-containing compound in the polymer matrix, where the Li-containing compound is a Li salt of a short-chain aliphatic acid. In addition, the scintillator material exhibits an optical response signature for thermal neutrons that is different than an optical response signature for fast neutrons.