A medical imaging system is provided. Imaging detector columns are installed in a gantry to receive imaging information about a subject. Imaging detector columns can extend and retract radially as well as be rotated orbitally around the gantry. The system can automatically adjust setup configuration and an imaging operation based on subject shape estimation information.

The invention relates to a combined detector (660) comprising a gamma radiation detector (100) and an X-ray radiation detector (661). The gamma radiation detector (100) comprises a gamma scintillator array (101.sub.x, y), an optical modulator (102) and a first photodetector array (103.sub.a, b) for detecting the first scintillation light generated by the gamma scintillator array (101.sub.x, y). The optical modulator (102) is disposed between the gamma scintillator array (101.sub.x, y) and the first photodetector array (103.sub.a, b) for modulating a transmission of the first scintillation light between the gamma scintillator array (101.sub.x, y) and the first photodetector array (103.sub.a, b). The optical modulator (102) comprises at least one optical modulator pixel having a cross sectional area (102′) in a plane that is perpendicular to the gamma radiation receiving direction (104). The cross sectional area of each optical modulator pixel (102′) is greater than or equal to the cross sectional area of each photodetector pixel (103′.sub.a, b).

The invention relates to a combined detector (660) comprising a gamma radiation detector (100) and an X-ray radiation detector (661). The gamma radiation detector (100) comprises a gamma scintillator array (101.sub.x, y), an optical modulator (102) and a first photodetector array (103.sub.a, b) for detecting the first scintillation light generated by the gamma scintillator array (101.sub.x, y). The optical modulator (102) is disposed between the gamma scintillator array (101.sub.x, y) and the first photodetector array (103.sub.a, b) for modulating a transmission of the first scintillation light between the gamma scintillator array (101.sub.x, y) and the first photodetector array (103.sub.a, b). The optical modulator (102) comprises at least one optical modulator pixel having a cross sectional area (102′) in a plane that is perpendicular to the gamma radiation receiving direction (104). The cross sectional area of each optical modulator pixel (102′) is greater than or equal to the cross sectional area of each photodetector pixel (103′.sub.a, b).

Scintillator products, apparatuses and methods are provided for use in autoradiographic imaging of a tissue sample excised from a subject. In particular, scintillator products and devices are provided that are substantially conformable to a surface of the excised tissue sample and configured to scintillate, in use, in response to radiation from a radiopharmaceutical administered to the subject in advance of the excision.

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.

The invention relates to a device for the detection of gamma rays (1) coming from a source (2) without image truncation and without image overlapping, comprising, at least, two detection cells (3) and each of said cells comprising a detection space (7) adapted to receive the gamma rays (1) that penetrate through an opening (5), wherein said detection space (7) comprises one or more detection assemblies (8, 8′), with some of said assemblies (8′) being positioned such that they stand in the way of the gamma rays (1) coming into the overlap volume (11) thereof.

A method for normalization of a positron emission tomography (PET) scanner. The PET scanner includes a plurality of blocks. Each of the plurality of blocks includes a plurality of rows. Each of the plurality of rows includes a plurality of actual detectors and an unused area. The method includes acquiring a plurality of lines of response (LORs) by scanning a normalization phantom, obtaining a plurality of actual counts by extracting a plurality of LORs subsets from the plurality of LORs and counting a number of elements in each LORs subset, generating a plurality of virtual detectors in each of the plurality of rows by assigning the unused area to the plurality of virtual detectors, generating a count profile for the plurality of actual detectors, estimating a plurality of virtual counts based on the count profile, and applying a normalization process on the plurality of blocks.

A correction X-ray detector according to an embodiment includes a plurality of detector elements configured to detect an X-ray, and processing circuitry. The processing circuitry is configured to acquire a plurality of output values respectively corresponding to the plurality of the plurality of detector elements. The processing circuitry is further configured to determine the detector elements to be used in generating correction data based on the plurality of output values.

Among other things, one or more techniques and/or systems are described for setting a sampling frequency for a radiation imaging system. The radiation imaging system comprises a rotating gantry configured to rotate a radiation source and a detector array about an object to generate an image(s) of the object. A data acquisition system is configured to sample the detector array as views. One or more flag structures are arranged according to a partial arc segment (e.g., a structure less than a full 360 degree circle). One or more sensors are disposed on one of the rotating gantry or a stationary support about which the rotating gantry rotates. When a sensor encounters a flag structure, a current rotational speed of the rotating gantry is determined. A clock frequency is updated based upon the current rotational speed to establish a sampling frequency for the data acquisition system for sampling the detector array.

A PET detector and method thereof are provided. The PET detector may include: a crystal array including a plurality of crystal elements arranged in an array and light-splitting structures set on surfaces of the plurality of crystal elements, the light-splitting structures jointly define a light output surface of the crystal array; a semiconductor sensor array, which is set in opposite to the light output surface of the crystal array and is suitable to receive photons from the light output surface, the semiconductor sensor array comprises a plurality of semiconductor sensors arranged in an array.