A flexible digital radiographic detector assembly includes a flexible sleeve enclosing a photosensor array supported by a flexible substrate. Integrated circuit readout electronics are coupled to the photosensor array. The digital radiographic detector assembly communicates with a local computer system or with a cloud server to transmit image data captured in the photosensor array, to display the image data on a screen, and to analyze defects that may be present in the image.

Embodiments of the present application provide a radiation detector module, a radiation detector, and an imaging device. In the radiation detector module, the number of radiation detector elements arranged in the Z direction of a circuit substrate is 4N rows or 4N+1 rows, N being an integer greater than or equal to 1. In this way, the radiation detector elements can be removed in a symmetric manner with respect to a center of the circuit substrate in the Z direction, for example, 2N rows of radiation detector elements are removed, such that the central position of the remaining radiation detector elements in the Z direction remains unchanged. Therefore, neither the positions of the remaining radiation detector elements nor the focus position of an X-ray source requires adjustment. Thus, no change of a gantry structure is required, and additional mechanical vibration is not caused, thereby ensuring imaging quality.

A PET apparatus is provided. The PET apparatus includes a scintillation array, a photosensor array, and processing circuitry. The scintillation array includes scintillator crystal units that are individually isolated with reflective material. Each scintillator crystal unit is configured to generate scintillation light in response to a gamma-ray interaction in the scintillator crystal unit that is caused by gamma-ray irradiation from an imaging object. Each scintillator crystal unit is configured with a substructure for decoding two or more depths within the scintillator crystal unit, such that gamma-ray interactions at different depths result in scintillation light that escapes from a light-escaping plane of the scintillator crystal unit with different patterns. The photosensor array is coupled to the scintillation array to convert the scintillation light received into electrical signals. The processing circuitry is configured to extract, from the electrical signals, information representing depth-of-interaction of the gamma-ray interactions in the scintillation array.

An X-ray detector for a computed tomography (CT) imaging system is provided. The X-ray detector includes a plurality of detector modules. Each detector module of the plurality of detector modules includes a scintillator layer configured to convert X-ray photons into lower energy light photons. Each detector module of the plurality of detector modules also includes a light imager layer configured to convert the light photons into electrons, wherein the light imager layer includes a light imager panel comprising an array of photodiodes. Each detector module of the plurality of detector modules further includes a readout device that converts the electrons into digitized pixel values, wherein each photodiode of the array of photodiodes is coupled to a respective dedicated readout channel of the readout device via a respective dedicated data line, and the readout device is configured to continuously directly readout the electrons from the array of photodiodes.

Systems and methods are herein provided for a radiation detector with rectangular pixels. In one example, an x-ray imaging system comprises a pixel array of a flat panel detector comprising a plurality of pixels with a rectangular pixel pitch arranged in pairs, wherein each of the plurality of pixels is configured to generate respective image data signals, wherein in low-dose applications, TFT control lines of pixels in each pixel pair are energized simultaneously to generate signals with an effective pixel pitch of twice the rectangular pixel pitch and in high-dose applications, TFT control lines of pixels in each pixel pair are energized sequentially and the detector is translated during image acquisition for an effective pixel pitch of half the rectangular pixel pitch.

A scintillator having a silicon photomultiplier (SiPM) embedded therein is described. The scintillator comprises an amorphous organic glass scintillator (OGS) material having a glass transition temperature above which the OGS material behaves as a supercooled or stable liquid, and a SiPM having a lead coupled thereto and having a temperature tolerance greater than the glass transition temperature of the OGS material. The SiPM is positioned in the OGS material while the OGS material is in a liquid state above the glass transition temperature, and the OGS material is cooled to an amorphous solid state below the glass transition temperature with the SiPM embedded therein.