Disclosed herein is a method comprising: capturing a first image of a tissue using radiation; selecting a region of the tissue based on the first image; capturing a second image of the tissue in the region using the radiation; wherein a signal-to-noise ratio of the second image is higher than a signal-to-noise ratio of the first image.

A system and method for delivering microbeam radiation therapy (MRT) includes a computed tomography scanner (“CT”) configured to generate tomographic images of a subject, or patient, the scanner including an imaging apparatus, a gantry with an opening for positioning the patient therein, an axis of rotation around which the gantry rotates, and an x-ray source mounted to and rotatable with the gantry. The system includes a bed for patient positioning within the gantry opening and a multi-slit collimator removably mounted downstream of the x-ray source for delivering an array of microbeams of MRT to a targeted portion of the patient. Switching between MRT and CT is provided, and MRT modes of operation include a stationary mode, and continuous and step-wise rotational modes.

A system and method for delivering microbeam radiation therapy (MRT) includes a computed tomography scanner (“CT”) configured to generate tomographic images of a subject, or patient, the scanner including an imaging apparatus, a gantry with an opening for positioning the patient therein, an axis of rotation around which the gantry rotates, and an x-ray source mounted to and rotatable with the gantry. The system includes a bed for patient positioning within the gantry opening and a multi-slit collimator removably mounted downstream of the x-ray source for delivering an array of microbeams of MRT to a targeted portion of the patient. Switching between MRT and CT is provided, and MRT modes of operation include a stationary mode, and continuous and step-wise rotational modes.

A whole body PET and CT combined detector and device, comprising a CT scanner frame (4) and a PET detection chamber (5) at the front and the rear along a common central axis. The CT scanner frame (4) is provided with a housing and also has a cylindrical CT scanning channel vertical to the central axis; the PET detection chamber (5) is formed by a plurality of PET detection modules (6, 7) adjacent to each other, and PET detection crystals (10) are all arranged in a direction towards to the chamber, the PET detection chamber (5) is entirely closed or a first opening is formed at the side adjacent to the CT scanner frame (4); each of the PET detection modules (6, 7) is composed of the PET detection crystals (10), a photoelectric sensor array (8), and a light guide (9); and except for the first opening, the cross-sectional areas of all gaps of the PET detection chamber (5) are smaller than the detected surface area of the smallest one of the PET detection crystals (10).

A whole body PET and CT combined detector and device, comprising a CT scanner frame (4) and a PET detection chamber (5) at the front and the rear along a common central axis. The CT scanner frame (4) is provided with a housing and also has a cylindrical CT scanning channel vertical to the central axis; the PET detection chamber (5) is formed by a plurality of PET detection modules (6, 7) adjacent to each other, and PET detection crystals (10) are all arranged in a direction towards to the chamber, the PET detection chamber (5) is entirely closed or a first opening is formed at the side adjacent to the CT scanner frame (4); each of the PET detection modules (6, 7) is composed of the PET detection crystals (10), a photoelectric sensor array (8), and a light guide (9); and except for the first opening, the cross-sectional areas of all gaps of the PET detection chamber (5) are smaller than the detected surface area of the smallest one of the PET detection crystals (10).

A method for verifying aperture positions of a pre-patient collimator of a computed tomography (CT) imaging system includes obtaining data collected by an X-ray measurement device having detector elements subjected to X-rays emitted from an X-ray source of the CT imaging system with the pre-patient collimator at an expected aperture position. The method also includes calculating a measured collimator aperture position for the pre-patient collimator based on the obtained data. The method further includes comparing the measured collimator aperture position to a system specification for the expected aperture position for the CT imaging system. The method even further includes generating an output based on the comparison of the measured collimator aperture position to the system specification.

A method for verifying aperture positions of a pre-patient collimator of a computed tomography (CT) imaging system includes obtaining data collected by an X-ray measurement device having detector elements subjected to X-rays emitted from an X-ray source of the CT imaging system with the pre-patient collimator at an expected aperture position. The method also includes calculating a measured collimator aperture position for the pre-patient collimator based on the obtained data. The method further includes comparing the measured collimator aperture position to a system specification for the expected aperture position for the CT imaging system. The method even further includes generating an output based on the comparison of the measured collimator aperture position to the system specification.

The present invention relates to optimizing values for scan parameters for a scan of an object. An object specific exposure time is determined based on a maximal required value of a z-dependent tube current by exposure time product along a z-axis of the object and a maximal available tube current value of a tube used for the scan of the object (140). The maximal available tube current value depends on a tube voltage and maximal electric power of the tube at given focal spot area (110) and the z-dependent tube current by exposure time product profile is based on a dose index value or a pixel noise index value for the scan of the object, the tube voltage, and a z-dependent object size along the z-axis (120). The object specific exposure time is used for determining values of the scan parameters for the scan of the object (150).

The present invention relates to optimizing values for scan parameters for a scan of an object. An object specific exposure time is determined based on a maximal required value of a z-dependent tube current by exposure time product along a z-axis of the object and a maximal available tube current value of a tube used for the scan of the object (140). The maximal available tube current value depends on a tube voltage and maximal electric power of the tube at given focal spot area (110) and the z-dependent tube current by exposure time product profile is based on a dose index value or a pixel noise index value for the scan of the object, the tube voltage, and a z-dependent object size along the z-axis (120). The object specific exposure time is used for determining values of the scan parameters for the scan of the object (150).

A mobile radiography apparatus has radio-opaque markers, each marker coupled to a portion of the mobile radiography apparatus, wherein each of the markers is in a radiation path that extends from an x-ray source or x-ray sources. A detector is mechanically uncoupled from the x-ray source or x-ray sources for positioning behind a patient. Processing logic is configured to calculate a detector position with relation to the x-ray source or x-ray sources according to identified marker positions in acquired projection images, and to reconstruct a volume image according to the acquired projection images.