In a conventional radiation capturing device, such as an X-ray device or a CT scanner, a structured surface part, e.g. a scintillator array, is used that is manufactured by mechanical processing, e.g. by dicing and grinding. In order to modifying the scintillating properties of a scintillating material, further manufacturing steps, such as high temperature cycling like sintering etc., are performed in order to restore or at least improve the scintillating properties. This application proposes to form a structured surface part with a particle-in-binder structure containing scintillator or other radiation-relevant particles, using additive manufacturing with a photosensitive mixture to form a layer-wise structure. Therefore, subsequent manufacturing steps, such as sintering, can be omitted. The structured surface part is bendable.

A scintillation cuvette for measuring ionizing radiation, the scintillation cuvette includes: a light guide structure with a light guide wall having a first refractive index; a window having a second refractive index, the first refractive index being lower than the second refractive index; and a scintillation medium situated in the scintillation cuvette, having a predefined refractive index that is higher than the first refractive index.

A scintillator panel includes a substrate, a resin protective layer formed on the substrate and made of an organic material, a barrier layer formed on the resin protective layer and including thallium iodide as a main component, and a scintillator layer formed on the barrier layer and including cesium iodide with thallium added thereto as a main component. According to this scintillator panel, moisture resistance can be improved due to the barrier layer provided therein.

The disclosure provides a first sensing device and a second sensing device. The second sensing device is disposed on the first sensing device, and each of the first sensing device and the second sensing device includes a substrate, a sensor array, and a scintillator layer. The sensor array is disposed on the substrate. The scintillator layer is disposed on the sensor array. A thickness of the scintillator layer of the second sensing device is greater than a thickness of the scintillator layer of the first sensing device.

Methods of scintillation, scintillation devices, and metal halide hybrids that may be used as X-ray scintillators. The metal halide hybrids may include organic metal halide hybrids, inorganic metal halide hybrids, or organic-inorganic metal halide hybrids. The metal halide hybrids may have a 0D structure. The metal halide hybrids may be in the form of one or more discrete crystals.

Systems and methods for digital X-ray imaging are disclosed. An example portable X-ray scanner includes: an X-ray detector configured to generate digital images based on incident X-ray radiation; an X-ray tube configured to output X-ray radiation; a computing device configured to control the X-ray tube, receive the digital images from the X-ray detector, and output the digital images to a display device; a power supply configured to provide power to the X-ray tube, the X-ray detector, and the computing device; and a frame configured to: hold the X-ray detector, the computing device, and the power supply; and hold the X-ray tube such that the X-ray tube directs the X-ray radiation to the X-ray detector.

A Cherenkov-based or thin-sheet scintillator-based imaging system uses a radio-optical triggering unit (RTU) that detects scattered radiation in a fast-response scintillator to detect pulses of radiation to permit capture of Cherenkov-light or scintillator-light images during pulses of radiation and background images at times when pulses of radiation are not present without need for electrical interface to the accelerator that provides the pulses of radiation. The Cherenkov images are corrected by background subtraction and used for purposes including optimization of treatment, commissioning, routine quality auditing, R&D, and manufacture. The radio-optical triggering unit employs high-speed, highly sensitive radio-optical sensing to generate a digital timing signal which is synchronous with the treatment beam for use in triggering Cherenkov light or scintillator light imaging.

Provided is a radiation detector having a portion in which a substrate in which a plurality of pixels for accumulating electric charges generated in accordance with light converted from radiation are formed in a pixel region, a conversion layer that converts radiation into light, a reflective pressure sensitive adhesive layer that reflects the light converted by the conversion layer, and an adhesive layer that covering a region including a region ranging from an end part of the pressure sensitive adhesive layer to a surface of the substrate are provided in this order.

An X-ray detector comprises a first scintillator layer, a second scintillator layer, a first photodiode array, a second photodiode array, and at least one light emitting layer. The first scintillator layer is configured to absorb X-rays from an X-ray pulse and emit light. The first photodiode array is positioned adjacent to the first scintillator layer and is configured to detect at least some of the light emitted by the first scintillator layer. The second scintillator layer is configured to absorb X-rays from the X-ray pulse and emit light. The second photodiode array is positioned adjacent to the second scintillator layer and is configured to detect at least some of the light emitted by the second scintillator layer. The at least one light emitting layer is configured to emit radiation such that at least some of the emitted radiation irradiates the first photodiode array, and at least some of the emitted radiation irradiates the second photodiode array.

The present disclosure provides an image sensor and electronic equipment. The image sensor includes: a pixel array, comprising a plurality of pixels, wherein a light-transmitting part is disposed between adjacent pixels; a protective layer, covering at least a part of a surface of the pixel; a conversion layer, configured to convert X-ray into visible light; wherein when X-ray is incident from a side of the image sensor, a portion of the X-ray is incident on the protective layer, another portion of X-ray transmits through the light-transmitting part between the pixels, reaches the conversion layer, and is converted into visible light by the conversion layer and received by the pixel. With the above solution, the pixels can be protected from the damage of X-ray high-energy photons while improving the resolution of the captured X-ray image.