Provided are a charged particle detector and a radiation detector capable of obtaining an observation image with correct contrast without saturation even when the number of signal electrons incident on a detector is increased due to an increase in the current of a primary electron beam. The charged particle detector is characterized by having a scintillator (109) having a signal electron detection surface (109a) for detecting signal electrons emitted when a specimen is irradiated with primary electrons and converting the signal electrons into light, a light detector (111) having a light detection surface (111a) for detecting the light emitted from the scintillator (109), and a light guide (110) disposed between the scintillator (109) and the light detector (111), wherein the area of the light detection surface (111a) is larger than the area of the signal electron detection surface (109a).

A scintillator panel is provided. The scintillator panel comprises: a support; a scintillator configured to generate light in accordance with incident radiation; a light reflecting layer arranged between the support and the scintillator and configured to reflect the light; a semi-transmissive layer arranged between the light reflecting layer and the scintillator and configured to reflect part of the light and transmit other part of the light; and an optical adjustment layer arranged between the light reflecting layer and the semi-transmissive layer and configured to make an optical distance between the light reflecting layer and the semi-transmissive layer become a length with which the light resonates.

An intraoral sensor includes an image sensor, an FOP, a scintillator, and a case. The FOP includes a first main surface, a second main surface, and a plurality of lateral surfaces. The first main surface and the second main surface have a polygonal shape. An edge of the second main surface is constituted by a plurality of corner portions, and a plurality of side portions connect the corner portions adjacent to each other. The scintillator is provided on the second main surface and the plurality of lateral surfaces in such a manner that the corner portions and the ridge portions constituted by the lateral surfaces adjacent to each other are exposed.

A radiation detector includes a wiring board, a first image sensor, a second image sensor, a first fiber optic plate, a second fiber optic plate, and a scintillator layer. The first fiber optic plate can guide light between a first light entering region and a first light exiting region. The second fiber optic plate can guide light between a second light entering region and a second light exiting region. One side of the first light entering region and one side of the second light entering region are in contact with each other. The first light exiting region is positioned on a first light receiving region. The second light exiting region is positioned on a second light receiving region. One side surface of a first side surface and one side surface of a second side surface exhibit shapes along each other and in contact with each other.

A scintillator unit is described for use in a radiation detector assembly comprising: a scintillator comprising a scintillating material; a wrapping layer at least partly covering an external surface of the scintillating material; wherein the wrapping layer comprises a composite layer including a first layer of diffusively reflective material and a second layer of specularly reflective material. A radiation detector assembly including a scintillator unit is also described. Methods of fabrication of the same are also described.

An apparatus including a scintillator arrangement including a plurality of optically isolated scintillators that extend lengthwise along a plurality of respective parallel axes and define respective scintillation channels, wherein each of the optically isolated scintillators extends lengthwise between an input interface and an output interface and is arranged to receive higher energy photons at the input interface, to convert high energy photons to lower energy photons, and to output lower energy photons from the output interface in a respective scintillation channel, wherein the optical isolation reduces transmission of lower energy photons between scintillation channels.

[Problem] Provided is a scintillator panel which is capable of imaging at a low dose while suppressing the contrast deterioration caused by scattered radiation, and further has improved luminance and MTF.

[Solving Means] A scintillator panel having a scintillator layer for converting radiation into light, characterized in that the scintillator layer is in direct contact on a photoelectric conversion element and includes a reflecting layer and a scattered radiation diffusing layer on a radiation incident side of the scintillator layer, the scattered radiation diffusing layer is present closer to the radiation incident side than the reflecting layer, and the scattered radiation diffusing layer has an X-ray transmittance of 99.5% or more.

According to one embodiment, a scintillator includes a first layer provided on a surface of a substrate and including thallium activated cesium iodide; and a second layer provided on the first layer and including thallium activated cesium iodide. The second layer includes crystals having a [100] orientation partially diverted from a direction perpendicular to the surface of the substrate. Half width at half maximum of a frequency distribution curve of an angle between the direction perpendicular to the surface of the substrate and the [001] orientation, which is obtained by measuring the angle using EBSD method, is 2.4 degree or less.

Provided is a radiation image detector, including: a substrate; an optical image detector located on the substrate; and a radiation conversion layer located above the optical image detector to convert radiation into visible light. The optical image detector includes a photosensitive pixel array formed by a plurality of photosensitive pixels arranged periodically; each photosensitive pixel includes a photoelectric conversion layer which is capable of converting the visible light into electric charges. The photoelectric conversion layer includes an active region and an inactive region. The active region occupies less than 70% of the area of the photoelectric conversion layer. Each photosensitive pixel further includes a light-guide layer located between the radiation conversion layer and the photoelectric conversion layer and configured to guide the visible light to the active region.

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.