The present disclosure provides a gamma ray imaging device and an imaging method, where the imaging device includes a plurality of separate detectors. The plurality of separate detectors are provided at an appropriate spatial position, in an appropriate arrangement manner and are of an appropriate detector material, such that when rays emitted from different positions in an imaging area reach at least one of the plurality of separate detectors, at least one of the thicknesses of the detectors, the materials of the detectors, and the numbers of the detectors though which the rays pass are different, thereby achieving the effect of determining the directions of rays.

A radiation imaging apparatus comprising a first scintillator, a second scintillator which receives radiation transmitted through the first scintillator, conversion elements and a controller is provided. The conversion elements include first conversion elements and second conversion elements with different sensitivities for detecting light emitted from at least one of the first scintillator or the second scintillator. During radiation irradiation, the controller obtains, from a signal output from one or more measuring element configured to measure a dose of incident radiation, a first signal corresponding to light converted from radiation by the second scintillator, and outputs, based on the first signal, a stop signal configured to stop the radiation irradiation, and after the radiation irradiation, the controller causes the first conversion elements and the second conversion elements to output signals configured to generate an energy subtraction image.

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.

Provided is a radiation image detector, including: a substrate; a continued radiation conversion layer configured to convert radiation into visible light; an optical image detector on the substrate and between the radiation conversion layer and the substrate, wherein the optical image detector comprises an array of photosensitive pixels; a light-shielding structure located on a side of the plurality of photosensitive pixels facing away from the substrate, wherein the light-shielding structure has a plurality of openings to allow the visible light to reach the photosensitive pixels; and a light-collecting structure located between the radiation conversion layer and the light-shielding structure and comprising a plurality of convex lenses, wherein each convex lens has its optical axis perpendicular to the light-shielding structure and passing through one of the plurality of openings.

Detector module designs for radiographic imaging include first and second layers of scintillator rods or pixel arrays oriented in first and second directions. The first and second directions are transversely oriented to define a light sharing region between the first and second layers. Encoding features may be disposed in, on or between the first and second layers, and configured to modulate propagation of optical signals therealong or therebetween.

Disclosed herein is a method comprising: forming electrical contacts on a first surface of an epitaxial layer supported on a substrate, the first surface being opposite from the substrate; bonding the epitaxial layer to an electronics layer, wherein the first surface faces the electronics layer and the electrical contacts on the first surface are bonded to electrical contacts of the electronics layer; exposing a second surface opposite the first surface by removing the substrate; and forming a common electrode on the second surface.

The disclosure is directed at a method and apparatus for a flat panel X-ray imaging detector. In one embodiment, the apparatus includes three (3) layers including a top layer, an intermediate layer and a bottom layer. The top layer generates a top layer image; the intermediate layer generates an intermediate layer image; and the bottom layer generates a bottom layer image. The intermediate layer also operates simultaneously as an intermediate X-ray energy filter.

Detector module designs for radiographic include first and second layers of scintillator rods or pixel arrays oriented in first and second directions. The first and second directions are transversely oriented to define a light sharing region between the first and second layers. Encoding features may be disposed in, on or between the first and second layers, and configured to modulate propagation of optical signals therealong or therebetween.

Detector module designs for radiographic imaging include first and second layers of scintillator rods or pixel arrays oriented in first and second directions. The first and second directions are transversely oriented to define a light sharing region between the first and second layers. Encoding features may be disposed in, on or between the first and second layers, and configured to modulate propagation of optical signals therealong or therebetween.

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.