Method and apparatus are disclosed for generating a scatter-corrected image from positron emission tomography (PET) or other radioemission imaging data (20) acquired of an object (12) in a field of view (14). A background portion (26B) of the PET imaging data is identified corresponding to a background region (14B) of the FOV that is outside of the object. An outside-FOV activity estimate (40) for at least one spatial region outside of the FOV and into which the object extends is adjusted (e.g. iterative or several randomly selected estimates) to optimize a simulated scatter distribution for the combination of the PET imaging data and the outside FOV activity estimate to match the background portion (26B) of the PET imaging data. The PET imaging data are reconstructed to generate a scatter-corrected PET image of the object in the FOV using the optimized simulated scatter distribution.

An apparatus and a method for detection of defective pixels for a photon-counting detector-based computed tomography (CT) system is disclosed. In particular, the apparatus and the method disclosed herein, detect detector pixels that have intermittent behavior using on-the-fly defective pixel screening based on various criteria during an object scan. The defective pixels are discarded using a defective pixel map before image reconstruction.

A radiation imaging apparatus that is operable in a plurality of imaging modes with different frame rates, and includes a radiation detection unit configured to obtain, based on a set imaging mode, a radiation image based on charges accumulated by radiation irradiation, includes: a collection control unit configured to set, based on a difference in frame rate in a combination of the set imaging mode and an imaging mode switched from the imaging mode, a collection time of an offset image for correcting an offset component of the radiation image; and an image obtainment unit configured to obtain the offset image based on the collection time.

A radiation image capture apparatus including a plurality of pixels which include a detection pixel configured to detect an irradiation amount and an exposure decision unit configured to decide an amount of radiation irradiated from a radiation generation apparatus. The exposure decision unit decides the amount of irradiated radiation based on an output of the detection pixel during radiation irradiation and a correction value that is an output of the detection pixel while the radiation irradiation is not performed. The exposure decision unit obtains the correction value after a read operation of a signal based on radiation during image capture is performed, and in the subsequent image capture, the amount of irradiated radiation is decided based on the output of the detection pixel during the radiation irradiation and the correction value.

A method for positron emission tomography (PET) imaging may include obtaining photon information of photons that are emitted from an object and detected by detector units of a detector of a PET scanner. The method may also include obtaining, based on the photon information and lines of response (LORs), more than one coincidence window width value of the PET scanner. The method may also include determining coincidence events of the photons based on the more than one coincidence window width value.

A quality assurance phantom configured for connection to a x-ray device including a housing member having an opening configured to receive a digital sensor, a frame member disposed within the housing member, the frame member configured to receive a phantom device, the phantom device comprising, a contrast layer configured to assess a contrast resolution, wherein the contrast layer is configured to provide two or more different contrast levels, and a spatial resolution test layer, wherein the spatial resolution test layer includes at least one trace disposed on a first surface of a substrate, and an attachment member configured to detachably secure the housing member to the x-ray device.

Disclosed are a detection collimation unit, a detection apparatus and a SPECT imaging system. The detection collimation unit includes: a scintillation crystal array configured to receive a gamma photon emitted by a radioactive source in a detected object; and a number of photoelectric devices configured to receive the gamma photon and converting the gamma photon into a digital signal. The scintillation crystal array includes a number of scintillation crystals. The number of scintillation crystals are arranged substantially in parallel and are spaced from each other. Each scintillation crystal has a side face configured to receive a ray emitted by the radioactive source and an end face. The number of photoelectric devices are coupled to the end faces of the number of scintillation crystals.

One or more example embodiments relates to an imaging system configured to record projection images, the imaging system comprising a detector unit; a radiation source, wherein the detector unit includes two detector elements arranged one behind the other, both of the two detector elements cover a same recording area, the two detector elements including a first detector element and a second detector element, and at least one of the radiation source or the detector unit is configured such that the second detector element is not saturated for sections of the recording area in which the first detector element is saturated during irradiation; and a data acquisition unit configured to record a first data set of the first detector element and to record a second data set of the second detector element such that first data set and the second data set are separable from one another.

A processor acquires a first radiation image and a second radiation image which are acquired by imaging a subject, based on radiation having different energy distributions, performs sharpness conversion processing on at least one of the first radiation image or the second radiation image to make sharpness of the first radiation image and the second radiation image uniform, and derives a component image in which a specific component in the subject is emphasized, based on the first radiation image and the second radiation image which are subjected to the sharpness conversion processing.

Mobile three-dimensional (3D) cadmium-zinc-telluride (CZT) radiation imager with aperture masks provide improved imaging speed and visual depth imaging capabilities, making the disclosed solutions suitable at least for intraoperative medical applications. A 3D CZT imager includes a plurality of CZT crystals configured to generate charge in response to incident radiation emitted from a radiated area within a portion of the anatomical body and one or more electrodes configured to collect the charge generated from the incident radiation and induce electrical signals in response to the collected charge. The 3D CZT imager further includes an aperture mask positioned between the plurality of CZT crystals and the radiation source/target being imaged. The mask includes openings being designed or configured for particular projections of a radiation distribution onto the plurality of CZT crystals. Solutions disclosed herein can generate localized 3D radiation image reconstructions in real-time or near real-time.