Medical detectors and medical imaging devices are provided. In one aspect, a medical detector includes: a photoelectric conversion device, a first crystal array layer disposed over the photoelectric conversion device, and a second crystal array layer disposed over the first crystal layer. The first crystal array layer includes a plurality of first scintillation crystals arranged in a first crystal array, and a first coupling medium being filled between every adjacent two of the first scintillation crystals. The second crystal array layer includes a plurality of second scintillation crystals arranged in a second crystal array, and a second coupling medium being filled between every adjacent two of the second scintillation crystals. A light transmittance of the second coupling medium is different from a light transmittance of the first coupling medium.

An X-ray detector includes a scintillation plate and sensors, the scintillation plate having a glass capillary array with scintillation material filling, wherein the glass capillary array with scintillation material filling is mated with two high volume, low cost, CMOS sensors, and wherein the glass capillary array is arranged diagonally to mate with active parts of the two high volume, low cost, CMOS sensors.

The invention relates to a combined detector (660) comprising a gamma radiation detector (100) and an X-ray radiation detector (661). The gamma radiation detector (100) comprises a gamma scintillator array (101.sub.x, y), an optical modulator (102) and a first photodetector array (103.sub.a, b) for detecting the first scintillation light generated by the gamma scintillator array (101.sub.x, y). The optical modulator (102) is disposed between the gamma scintillator array (101.sub.x, y) and the first photodetector array (103.sub.a, b) for modulating a transmission of the first scintillation light between the gamma scintillator array (101.sub.x, y) and the first photodetector array (103.sub.a, b). The optical modulator (102) comprises at least one optical modulator pixel having a cross sectional area (102′) in a plane that is perpendicular to the gamma radiation receiving direction (104). The cross sectional area of each optical modulator pixel (102′) is greater than or equal to the cross sectional area of each photodetector pixel (103′.sub.a, b).

A gamma-ray detector includes a plurality of modular one-dimensional arrays of monolithic detector sub-modules. Each monolithic detector sub-module includes a scintillator layer, a light-spreading layer, and a photodetector layer. The photodetector layer comprises a two-dimensional array of photodetectors that are arranged in columns and rows. A common printed circuit board is electrically coupled to the two-dimensional array of photodetectors of the plurality of modular one-dimensional arrays of monolithic detector sub-modules of a corresponding modular one-dimensional array. The two-dimensional array of photodetectors can be electrically coupled in a split-row configuration or in a checkerboard configuration. The two-dimensional array of photodetectors can also have a differential readout.

A sensing substrate and an electronic device are provided. The sensing substrate includes a sensing unit on a base substrate. The sensing unit includes a sensing element and a conductive pattern, the sensing element has a light incident surface and a back surface that are opposite and a side surface between the light incident surface and the back surface. The conductive pattern is on a side of the sensing element away from the base substrate, and has a hollow portion and a transparent conductive portion surrounding the hollow portion, an orthographic projection of the hollow portion on the base substrate is at least partially within an orthographic projection of the sensing element on the base substrate, and an orthographic projection of the transparent conductive portion on the base substrate at least partially overlaps with an orthographic projection of the side surface of the sensing element on the base substrate.

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 computed tomography (CT) detector array (120) includes a monolithic scintillator (124). The monolithic scintillator includes at least a first scintillator region (202), a second scintillator region (206), and an optically reflective barrier (210) therebetween. The detector array is configured to detect X-ray radiation traversing an examination region and impinging the monolithic scintillator and generate first projection data indicative of an energy of x-ray radiation absorbed by the first scintillator region and second projection data indicative of an energy of x-ray radiation traversing the first scintillator and absorbed by the second scintillator region.

An X ray device, including an array substrate, a scintillator layer, a first adhesion layer, a function film, and a second adhesion layer, is provided. The scintillator layer is disposed on the array substrate. The first adhesion layer is disposed between the scintillator layer and the array substrate. The function film is disposed on the array substrate. The second adhesion layer is disposed between the function film and the array substrate. The function film covers the scintillator layer.

A radiation detecting device in which defective adhesion between an adhesive member and end portions of a plurality of sensor substrates is reduced. A radiation detecting device includes a plurality of sensor substrates disposed adjacent to each other, each sensor substrate including a side surface that connects a first surface, where a plurality of photoelectric converting elements are arranged in an array, and an opposing second surface to each other; a scintillator disposed at a side of the first surfaces of the plurality of sensor substrates; and a sheet-like adhesive member for adhering the plurality of sensor substrates and the scintillator to each other, wherein, between the plurality of sensor substrates, the sheet-like adhesive member adheres to the first surfaces and at least portions of the side surfaces such that the sheet-like adhesive member extends and continuously adheres from the first surfaces to the at least portions of the side surfaces.

The present specification discloses a system that employs a shutter-less method of measuring afterglow, in which the start and termination of the stimulating radiation from the radiation source is controlled electronically. A fast decay scintillator may be used in the beam path to monitor and track the rise and fall of the stimulating radiation to determine the dose and full cessation of the stimulating radiation. This information is used to calculate the afterglow for a slow decay scintillator. This method can also be used to calibrate and normalize scanned image data and produce an enhanced image. The fast decay scintillator is used as a monitoring or tracking device to be able to determine radiation source decay.