Various methods and systems are provided for an imaging detector array. In one example, a detector module of the array has an X-ray sensor assembly coupled to an upper surface of a conductive block and at least one integrated circuit positioned in a recess of the conductive block below the X-ray sensor assembly. The detector module may further include a radiation blocker positioned between the X-ray sensor assembly and the at least one integrated circuit.

Provided is a CZT semiconductor activity meter and an activity measuring device, which relate to the field of medical apparatus and instruments. The CZT semiconductor activity meter includes a shell, a CZT probe, a package substrate and a processing module, wherein the CZT probe is arranged on an end of the shell, the package substrate is arranged at the middle part of the shell and abuts against an inner wall of the shell, the CZT probe is connected to one side of the package substrate, the other side of the package substrate and the inner wall of the shell together form a package inner cavity, and the processing module is accommodated in the package inner cavity and connected to the package substrate. The CZT semiconductor activity meter has a small volume, is convenient to operate, does not require manual control during detection, and can be used at room temperature.

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 detection device includes a plurality of field effect transistors (FETs) arranged to form a resonant cavity. The cavity includes a first end and a second end. The plurality of FETs provide an electromagnetic field defining an standing wave oscillating at a resonant frequency defined by a characteristic of the cavity. A radiation input passing through the cavity induces a perturbation of the electromagnetic field.

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.

Disclosed herein is a method comprising: obtaining a third image from a first X-ray detector when the first X-ray detector and a second X-ray detector are misaligned; determining, based on a shift between a first image and the third image, a misalignment between the first X-ray detector and the second X-ray detector when the first and second detectors are misaligned; wherein the first image is an image the first X-ray detector should capture if the first and the second detectors are aligned.

A radiation detector includes a halide semiconductor sandwiched a cathode and an anode and a buffer layer between the halide semiconductor and the anode. The anode comprises a composition selected from: (a) an electrically conducting inorganic-oxide composition, (b) an electrically conducting organic composition, and (c) an organic-inorganic hybrid composition. The buffer layer comprises a composition selected from: (a) a composition distinct from the composition of the anode and including at least one other electrically conducting inorganic-oxide composition, electrically conducting organic composition, or organic-inorganic hybrid composition; (b) a semi-insulating layer selected from: (i) a polymer-based composition; (ii) a perovskite-based composition; (iii) an oxide-semiconductor composition; (iv) a polycrystalline halide semiconductor; (v) a carbide, nitride, phosphide, or sulfide semiconductor; and (vi) a group II-VI or III-V semiconductor; and (c) a component metal of the halide-semiconductor.

The present invention relates to a photon counting detector comprising a first direct conversion layer (10) comprising a low-absorption direct conversion material (11) for converting impinging high-energy electromagnetic radiation (100) into a first count signal and first electrical contacts (12), a second direct conversion layer (20) comprising a high-absorption direct conversion material (21) for converting impinging high-energy electromagnetic radiation (100) into a second count signal and second electrical contacts (22), said high-absorption direct conversion material having a higher absorption than said low-absorption direct conversion material, and a carrier layer (30, 30a, 30b) comprising first and second terminals (31, 32) in contact with the first and second electrical contacts and processing circuitry (35) configured to correct, based on the first count signal, the second count signal for errors, wherein said first direct conversion layer and the second direct conversion layer are arranged such that the high-energy electromagnetic radiation transmits the first direct conversion layer before it hits the second direct conversion layer.

To optimize image quality and/or sensitivity, a Compton camera is adaptable. The scatter and/or catcher detectors may move closer to and/or further away from a patient and/or each other. This adaptation allows a balancing of image quality and sensitivity by altering the geometry.

To capture more emitted photons with a Compton camera, the scatter detector is tilted (non-orthogonal angle) relative to a radial from the isocenter of the imaging system. The tilt creates a greater volume for scatter interaction. To capture more scatter photons, the catcher detector is non-planar, such as a multi-faced detector at least partially surrounding a volume behind the scatter detector. The tilted scatter detector alone, the non-planar catcher detector alone, or the tilted scatter detector and the non-planar catcher detector are used in the Compton camera.