An imaging system based on an imaging device and/or a cooling system is provided. The imaging system may include a control module, an imaging device, and/or a cooling system. The imaging device may include a first portion and a second portion. The cooling system may include a cooling module configured to generate a cooling medium, and/or a cooling medium passage configured to spread the cooling medium. The cooling medium passage may belong to a closed loop. At least part of the cooling system may be located within the imaging device such that the cooling medium may be in direct contact with the at least part of the imaging device.

Aspects of the subject disclosure may include, for example, a device comprising: a first micro-camera-element comprising a first sensor area and a first aperture element, the first aperture element having a first structural configuration, the first aperture element and the first sensor area being disposed relative to each other in order to cooperate in obtaining first imaging data having first characteristics, and the first characteristics comprising first imaging resolution and first angular coverage; a second micro-camera-element comprising a second sensor area and a second aperture element, the second aperture element having a second structural configuration, the second aperture element and the second sensor area being disposed relative to each other in order to cooperate in obtaining second imaging data having second characteristics, the second characteristics comprising second imaging resolution and second angular coverage, and the first imaging resolution differing from the second imaging resolution, the first angular coverage differing from the second angular coverage, or any combination thereof. Additional embodiments are disclosed.

To optimize image quality and/or sensitivity, a Compton camera is adaptable. The scatter and/or catcher detectors may move closer to and/or further away from a patient and/or each other. This adaptation allows a balancing of image quality and sensitivity by altering the geometry.

A radiation detection device (300) is used in a nuclear medicine diagnosis apparatus, and includes a plurality of scintillators (44), a semiconductor light-receiving device (SiPM), a position detection circuit (214), and a timing detection circuit (216). Each of the scintillators converts a gamma ray emitted from a subject (15) into fluorescence. The semiconductor light-receiving device is provided corresponding to each of the scintillators and converts the fluorescence converted by a corresponding one of the scintillators into an electrical signal. The position detection circuit specifies a gamma ray detection position in the scintillators based on the electrical signal from the semiconductor light-receiving device. The timing detection circuit is connected to an anode of the semiconductor light-receiving device, and specifies time information corresponding to a time of occurrence of an event in which the gamma ray is detected.

Methods and systems are provided for a medical imaging system having a detector array. In one example, the detector array may include a plurality of adjustable imaging detectors arranged in subsets thereof, each of the plurality of adjustable imaging detectors including a detector unit, each detector unit having a plurality of rows of detector modules, wherein the plurality of adjustable imaging detectors may be arranged on an annular gantry, where an inner surface of the annular gantry may circumscribe a substantially rectangular aperture therethrough, and wherein each subset of the plurality of adjustable imaging detectors may be respectively disposed on a side of the inner surface and may extend within the substantially rectangular aperture.

A method and apparatus are provided for nonlinear energy correction of a gamma-ray detector using a calibration spectrum acquired from the background radiation of lutetium isotope 176 (Lu-176) present in scintillators in the gamma-ray detector. Further, by periodically acquiring Lu-176 spectra using the background radiation from the scintillators, the nonlinear energy correction can be monitored to detect when changes in the gamma-ray detector cause the detector to go out of calibration, and then use a newly acquired Lu-176 spectrum to update the calibration of the nonlinear energy correction as needed. The detector calibration is performed by comparing a reference histogram to a calibration histogram generated using the nonlinear energy correction, and adjusting the parameters of the nonlinear energy correction until the two histograms match. Alternatively, the detector calibration is performed by comparing reference and calibration values for specific spectral features, rather than for the whole Lu-176 spectrum.

A radiation detector assembly is provided that includes a semiconductor detector, plural pixelated anodes disposed on a surface of the semiconductor detector, and at least one processor. Each pixelated anode is configured to generate a mixed primary signal responsive to reception of a photon by at least one surrounding anode of the pixelated anode and to generate a mixed secondary signal responsive to reception of a photon by the pixelated anode. The at least one processor is operably coupled to the pixelated anodes, and is configured to: acquire the mixed primary signal from a first pixelated anode; acquire the mixed secondary signal from a second pixelated anode; and count an event in the second pixelated anode responsive to acquiring the mixed primary signal from the first pixelated anode and the mixed secondary signal from the second pixelated anode.

Measuring in a first semiconductor crystal two anode channels and two cathode channels and measuring in a second semiconductor crystal one anode channel and one cathode channel; responsive to an energy of a sum of the two anode channels being within an energy window and an energy of the one anode channel being within the energy window: separating the two anode channels and the two cathode channels into combinations of anode-cathode channel pairs; for each of the anode-cathode channel pairs, determining a respective direction difference angle, each respective direction difference angle being determined via use of the one anode channel and one cathode channel; determining a determined one of the direction difference angles that has a smallest value; and setting as an initial interaction position of a photon a selected one of the anode-cathode channel pairs that corresponds to the determined direction difference angle. Additional embodiments are disclosed.

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 data processing apparatus according to an embodiment includes acquisition circuitry and specification circuitry. The acquisition circuitry is configured to acquire a detector signal containing a first component that is based on Cherenkov light and a second component that is based on scintillation light. The specification circuitry is configured to specify timing information about generation of the detector signal by curve fitting to the first component.