A radiographic imaging apparatus in which a radiation source, a plurality of gratings and a radiation detector are provided side by side in a radiation irradiation axis direction includes a hardware processor. The hardware processor generates a reconstructed image on the basis of a Moire fringe image obtained by performing imaging by irradiating a subject disposed at a position overlapping the radiation irradiation axis direction with radiation by the radiation source, acquires relative position information that is relative positions in two or more dimensions of the subject with respect to the gratings, and associates the reconstructed image with the relative position information.

A non-spectral computed tomography scanner includes a radiation source configured to emit x-ray radiation, a detector array configured to detect x-ray radiation and generate non-spectral data, and a memory configured to store a spectral image module that includes computer executable instructions including a neural network trained to produce spectral volumetric image data. The neural network is trained with training spectral volumetric image data and training non-spectral data. The non-spectral computed tomography scanner further includes a processor configured to process the non-spectral data with the trained neural network to produce spectral volumetric image data.

Single X-ray grating differential phase contrast (DPC) X-ray imaging is provided by replacing the conventional X-ray source with a photo-emitter X-ray source array (PeXSA), and by replacing the conventional X-ray detector with a photonic-channeled X-ray detector array (PcXDA). These substitutions allow for the elimination of the G0 and G2 amplitude X-ray gratings used in conventional DPC X-ray imaging. Equivalent spatial patterns are formed optically in the PeXSA and the PcXDA. The result is DPC imaging that only has a single X-ray grating (i.e., the G1 X-ray phase grating).

Systems and methods monitoring progress of procedures by radiation exposure are provided. Position data is received for an equipment item used for the procedure and configured to produce radiation (“radiation device”). Position data is received from the tracking device during the procedure. An estimated exposure level is determined by a controller for the individual based, at least in part, on the position data from the tracking device relative to the position data from the radiation device and compared to a benchmark. If the estimated exposure level for the individual exceeds the benchmark, an electronic notification is generated.

The invention is directed to a method for correcting scattered radiation in a computed tomography apparatus, wherein x-ray radiation emanating from an x-ray radiation source is divided into a plurality of partial beams by a grid structure such that irradiated regions and non-irradiated regions alternate, wherein a grid position of the grid structure is changed parallel to a detector surface. In a changed grid position, previously non-irradiated regions are irradiated and previously irradiated regions are not irradiated, wherein at least one radiograph of the test object is captured for each of the grid positions, wherein the radiographs captured at different grid positions are used to generate a bright field radiograph from the respectively irradiated regions and a dark field radiograph from the respectively non-irradiated regions and wherein a corrected radiograph is generated on the basis of the bright field radiograph and the dark field radiograph.

Various methods and systems are provided for scatter correction in nuclear medicine imaging systems. In one embodiment, a method for NM imaging comprises acquiring, with a plurality of detectors, imaging data separated into a high energy window and a low energy window, removing photopeak photons from the imaging data in the low energy window to obtain a corrected scatter distribution, correcting the imaging data based on the corrected scatter distribution, and outputting a scatter-corrected image reconstructed from the corrected imaging data. In this way, fast and accurate scatter correction for CZT-based gamma cameras may be performed, and image quality as well as quantitative accuracy may be increased.

An imaging method and device are described for improving the performance of a gamma camera by optimizing a figure of merit that depends upon cost, efficiency, and spatial resolution. In a modular gamma camera comprising a tiled array of gamma detector modules, the performance figure of merit can be optimized by sparsely placing gamma detector modules within the gamma camera, optimizing collimation, and providing means for detector and/or collimator motion. Sparse gamma cameras can be constructed as flat or curved panels, and elliptical or circular rings.

An X-ray CT apparatus according to an embodiment includes processing circuitry. The processing circuitry is configured to detect X-rays that have passed through a subject by using a detector and to acquire projection data on a basis of a detection result. The processing circuitry is configured to obtain position information of a highly X-ray absorbent member in the body of the subject. The processing circuitry is configured to derive information about transmission paths of the X-rays in accordance with a processing effect of an artifact reducing process performed on the highly X-ray absorbent member, on the basis of the position information of the highly X-ray absorbent member.

Disclosed is a way to provide a medical image processing device that may include a hardware processor that calculates at least one of trabecular connectivity, trabecular width, trabecular number, mineralization degree, osteoid volume, cortical width, and cortical porosity as a bone characteristic indicator of a subject from reconstructed image data generated from moiré image data acquired by photographing the subject.

A multi-modality imaging system allows for selectable photoelectric effect and/or Compton effect detection. The camera or detector is a module with a catcher detector. Depending on the use or design, a scatter detector and/or a coded physical aperture are positioned in front of the catcher detector relative to the patient space. For low energies, emissions passing through the scatter detector continue through the coded aperture to be detected by the catcher detector using the photoelectric effect. Alternatively, the scatter detector is not provided. For higher energies, some emissions scatter at the scatter detector, and resulting emissions from the scattering pass by or through the coded aperture to be detected at the catcher detector for detection using the Compton effect. Alternatively, the coded aperture is not provided. The same module may be used to detect using both the photoelectric and Compton effects where both the scatter detector and coded aperture are provided with the catcher detector. Multiple modules may be positioned together to form a larger camera, or a module is used alone. By using modules, any number of modules may be used to fit with a multi-modality imaging system. One or more such modules may be added to another imaging system (e.g., CT or MR) for a multi-modality imaging system.