A hybrid TOF-PET/CT tomograph comprising a detection chamber, gamma radiation detectors, X-ray detectors and a movable X-ray source, wherein the gamma radiation detectors (150, 250, 350, 450, 550) and the X-ray detectors (170, 270, 370, 470, 570) surround the detection chamber (102, 202, 302, 402, 502) around the whole perimeter of the detection chamber (102, 202, 302, 402, 502), and wherein the gamma radiation detectors (150, 250, 350, 450, 550) are located closer to the longitudinal axis (115, 215, 315, 415, 515) of the detection chamber (102, 202, 302, 402, 502) than the X-ray detectors (170, 270, 370, 470, 570), and wherein the gamma radiation detectors (150, 250, 350, 450, 550) comprise polymer strips (151, 251, 351, 451, 551) made of a scintillation material having a density lower than the density of the X-ray radiation detectors (171, 271, 371, 471, 571).

The invention relates to a hybrid medical PET-SPECT/MR imaging device comprising at least one scintillating crystal and at least one module for detecting radiation which contains at least one matrix of photodetectors and an electronics section, such that said module has a mechanical structure, the external, internal or both surfaces of which are divided into at least two sections, of which at least one is coated in graphene, and the rest in non-ferromagnetic conductive material, or all the sections are coated in graphene, and such that the coating forms a Faraday cage. The invention also relates to a shielding against radiofrequency for a medical imaging device, comprising a graphene coating, which is continuous or in bands, on all the faces of the mechanical structure of the detection module of the device, or a graphene coating, continuous or in bands, on at least one face, combined with a coating of non-ferromagnetic conductive materials on the remaining faces, and said shielding forming a Faraday cage.

In capturing an image of a grid by an image detector, a measurement pixel that is not in the position of a specific point having a maximum or minimum value of an output signal is referred to as a first measurement pixel, and a measurement pixel that is in the position of the specific point is referred to as a second measurement pixel. The disposition of the first and second measurement pixels are determined so as to satisfy the following condition: fG/fN≠odd number, wherein fG is a grid frequency and fN is a Nyquist frequency of pixels; and in shifting the grid C times by one pixel, the number of the first measurement pixels is larger than that of the second measurement pixels at any time in the range of a cycle C of a repetition pattern appearing in the image.

A multimodal imaging apparatus (1a, 1b) including scintillator elements (31) for capturing incident gamma quanta (25, 61) and for emitting scintillation photons (26) in response to said captured gamma quanta (25, 61). Photosensitive elements (33) capture the emitted scintillation photons (26) and determine a spatial distribution of the scintillation photons. The imaging apparatus (1a, 1b) is configured to be switched between a first operation mode for detecting low energy gamma quanta and a second operation mode for detecting high energy gamma quanta. The scintillator elements are arranged to capture incident gamma quanta (25, 61) from the same area of interest (65) in both operation modes. The scintillator elements (31) include a first region with high energy scintillator elements (27) for capturing high energy gamma quanta and a second region with low energy scintillator elements (29) for capturing low energy gamma quanta. A positioning mechanism (35) changes the orientation of the scintillator elements (31), in particular for tilting the scintillator elements (31), to switch between operation modes.

A surgical guidance system offering different levels of imaging capability while maintaining the same hand-held convenient small size of light-weight intra-operative probes. The surgical guidance system includes a second detector, typically an imager, located behind the area of surgical interest to form a coincidence guidance system with the hand-held probe. This approach is focused on the detection of positron emitting biomarkers with gamma rays accompanying positron emissions from the radiolabeled nuclei.

An image detector is disposed behind a grid. The image detector has normal pixels and measurement pixels. Out of a group of measurement pixels based on which an average value of dose measurement signals is calculated, a [C/D] number of measurement pixels are disposed or chosen in a cycle Z=(R×C)±D. Wherein, C represents a cycle of a repetition pattern appearing in an arrangement direction of X-ray transparent layers and X-ray absorbing layers in an X-ray image of the grid, and is represented in units of the number of pixels. R represents a natural number of 0 or more. D represents an integer less than the cycle C. [C/D] represents a maximum integer equal to or less than C/D. Provided that at least the [C/D] number of measurement pixels are shifted C occasions by one pixel, if D=1, the average value of the dose measurement signals is invariable without any variations.

An probe body comprising:

one or more light sources; one or more light sensors; an x-ray detector configured to detect, using at least one of the one or more light sensors, light from a scintillator for converting extra-orally applied x-rays to light; and a lower energy light detector configured to detect, using at least one of the one or more light sensors, light from an object illuminated by at least one of the one or more light sources.

Three semiconductor detectors are installed at positions where incidence of radiation on a scintillation detector is not blocked, at equal intervals centered on a central axis of the scintillation detector and at equal angles with respect to a plane which is at a right angle to the central axis. An energy compensation factor is determined on the basis of an average pulse height value obtained from a second pulse height spectrum obtained by analog voltage pulses which are output from these semiconductor detectors, and energy characteristics of a high-range dose rate obtained by a direct-current voltage which is output from the scintillation detector are compensated for.

An integrated microtomography and optical imaging system includes a rotating table that supports an imaging object, an optical stage, and separate optical and microtomography imaging systems. The table rotates the imaging object about a vertical axis running therethrough to a plurality of different rotational positions during a combined microtomography and optical imaging process. The optical stage can be a trans-illumination, epi-illumination or bioluminescent stage. The optical imaging system includes a camera positioned vertically above the imaging object. The microtomography system includes an x-ray source positioned horizontally with respect to the imaging object. Optical and x-ray images are both obtained while the imaging object remains in place on the rotating table. The stage and table are included within an imaging chamber, and all components are included within a portable cabinet. Multiple imaging objects can be imaged simultaneously, and side mirrors can provide side views of the object to the overhead camera.

A radioemission scanner (12) is operated to acquire tomographic radioemission data of a radiopharmaceutical in a subject in an imaging field of view (FOV). An imaging system is operated to acquire extension imaging data of the subject in an extended FOV disposed outside of and adjacent the imaging FOV along an axial direction (18). A distribution of the radiopharmaceutical in the subject in the extended FOV is estimated based on the extension imaging data, and further based on a database (32) of reference subjects. The tomographic radioemission data are reconstructed to generate a reconstructed image (26) of the subject in the imaging FOV. The reconstruction includes correcting the reconstructed image for scatter from the extended FOV into the imaging FOV based on the estimated distribution of the radiopharmaceutical in the subject in the extended FOV.