A radiation imaging apparatus comprises a generating unit configured to generate a material characteristic image with respect to a plurality of materials included in a radiation image that has been captured using different radiation energies; and a reconstructing unit configured to set different radiation energies for the respective plurality of materials, and to generate a reconstructed image based on monochromatic radiation images of the respective materials, the monochromatic radiation images being based on the different radiation energies.

Various noncollimated single photon emission computed tomography (SPECT) technologies are described herein. An example device includes an array of detectors configured to detect a flux of first photons transmitted from a field of view (FOV) over time. The device also includes an attenuator disposed between the array of detectors and the FOV. The attenuator is configured to move over time and to attenuate second photons emitted from the source. In various implementations, the attenuator is not a collimator. Based on the fluxes of the first photons detected by the detectors, and the position of the attenuator over time, an imaging system may be configured to generate an image of the FOV.

A display control unit displays a medical image from which at least one region of interest is extracted on a display unit. A correction unit corrects a boundary of the region of interest according to a correction instruction for the boundary of the region of interest extracted from the displayed medical image. An image generation unit generates a weighted image in which each pixel in the medical image has, as a pixel value of each pixel, a weight coefficient representing a weight of being within the region of interest, by setting an initial weight coefficient for the extracted region of interest and setting a corrected weight coefficient for a corrected region for which the correction instruction is given in the medical image.

A method is provided for updating a uniformity map of a detector. The detector defines a detector surface area. The method includes positioning a flood on a sub-portion of the detector surface area of the detector. The flood defines a flood area that is smaller than the detector surface area. Also, the method includes collecting counts from the flood for the sub-portion of the detector surface area. Further, the method includes updating an adjustment portion of the uniformity map using the counts collected for the sub-portion of the detector surface area, wherein the adjustment portion corresponds to at least a part of the sub-portion of the detector surface area.

A method is provided for updating a uniformity map of a detector. The detector defines a detector surface area. The method includes positioning a flood on a sub-portion of the detector surface area of the detector. The flood defines a flood area that is smaller than the detector surface area. Also, the method includes collecting counts from the flood for the sub-portion of the detector surface area. Further, the method includes updating an adjustment portion of the uniformity map using the counts collected for the sub-portion of the detector surface area, wherein the adjustment portion corresponds to at least a part of the sub-portion of the detector surface area.

A PET detecting module may include a scintillator array configured to receive a radiation ray and generate optical signals in response to the received radiation ray. The scintillator array may have a plurality of rows of scintillators arranged in a first direction and a plurality of columns of scintillators arranged in a second direction. A first group of light guides may be arranged on a top surface of the scintillator array along the first direction. The light guide count of the first group of light guides may be less than the row count of the plurality of rows of scintillators. A second group of light guides may be arranged on a bottom surface of the scintillator array. The light guide count of the second group of light guides may be less than the column count of the plurality of columns of scintillators.

An intraoperative imaging system combines a gamma probe and an ultrasound probe. The probes are linked to provide co-registration of gamma radiation detected by the gamma probe with an image acquired by the ultrasound probe. The gamma probe has a converging collimator made of a metal block having a plurality of channels therein, which converge from an output face toward an input face. Each channel extends between and opens out at the faces such that openings at the input face have smaller cross-sectional areas than openings at the output face so that each channel tapers inwardly from the output face to the input face. The collimator has an external focal point distant from the input face. The system improves identification and localization of cancerous cells, facilitating more accurate biopsy data and more complete surgical resection. The gamma probe increases sensitivity, while maintaining spatial resolution, and increasing depth of view.

An intraoperative imaging system combines a gamma probe and an ultrasound probe. The probes are linked to provide co-registration of gamma radiation detected by the gamma probe with an image acquired by the ultrasound probe. The gamma probe has a converging collimator made of a metal block having a plurality of channels therein, which converge from an output face toward an input face. Each channel extends between and opens out at the faces such that openings at the input face have smaller cross-sectional areas than openings at the output face so that each channel tapers inwardly from the output face to the input face. The collimator has an external focal point distant from the input face. The system improves identification and localization of cancerous cells, facilitating more accurate biopsy data and more complete surgical resection. The gamma probe increases sensitivity, while maintaining spatial resolution, and increasing depth of view.

A radiation monitoring device 1 includes a scintillator portion 10 which emits light whose intensity depends on a dose of incident radiation, an optical fiber 20 which transmits photons generated in the scintillator portion 10, a photoelectric converter 30 which converts photons transmitted by the optical fiber 20 to electric signals, a signal counter 40 which counts each of electric signals after being converted by the photoelectric converter 30 with a certain dead time adjusted relative to time width of an irradiation pulse of radiation, a dose calculation unit 50 which calculates a dose from a signal count value counted by the signal counter 40, and a display unit 60 which displays a result of measurement calculated by the dose calculation unit 50.

In an embodiment of the present disclosure, in order to raise the reproducibility of a reconstructed tomographic image without increasing a calculation load, any one among two directions adjacent to two boundaries that demarcate an angular scan range is offset from any one among coordinate axes of a two-dimensional tomographic image of N pixels×N pixels, and the angle of the offset is made to be above 0 degrees and under 90 degrees or above −90 degrees and under 0 degrees. A detection device, which includes N detection elements, performs detection in each detection direction, and a first vector having N×N elements is obtained from a detection signal obtained by the detection device in a detection operation. A discrete Inverse Radon transform matrix is applied to the first vector to obtain a second vector having N×N elements. The second vector is de-vectorized to obtain image data for a two-dimensional tomographic image of N pixels×N pixels. An inverse matrix of a system matrix for an offset is obtained and used as the discrete Inverse Radon transform matrix.