Detector modules, detectors and medical imaging devices are provided. One of the detector modules includes: a support and a plurality of detector sub-modules arranged on the support along an extension direction in which the support extends. Each of the detector sub-modules has a first area and a second area in the extension direction. A detecting device is disposed in the first area, and a functional module is disposed in the second area. The functional module is electrically connected to the detecting device for receiving an electrical signal from the detecting device. The plurality of detector sub-modules includes a first detector sub-module and a second detector sub-module that are arranged adjacent to each other in the extension direction, and the first area of the first detector sub-module at least partially overlaps with the second area of the second detector sub-module.

An imaging system is provided. A method for installing the imaging system is provided. The imaging system may include a first modality imaging apparatus. The first modality imaging apparatus may have a detector including a scintillator unit, a photodetector unit, a circuit unit, a supporting block, and a supporting board. The supporting block may be disposed on an end of the scintillator unit. The supporting board may be disposed between the photodetector unit and the circuit unit.

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.

Provided is a PET scanner system having a PET scanner gantry that is configured for delivering a uniformly distributed cooling air to a plurality of detectors housed in the PET scanner gantry. The PET scanner gantry includes a cooling air delivery manifold that includes a patient tunnel portion; and a front funnel portion. The front funnel portion includes an annular interior wall defining an entry opening of the patient tunnel portion; and an air plenum has an annular structure for carrying a flow of pressurized cooling air received from a remote source supplements the pressurized cooling air with a supply of ambient air and directs it to the plurality of detectors.

The application provides a three-dimensionally heterogeneous PET system comprising at least two heterogeneous detector modules, each comprising at least two kinds of crystal strips closely arranged to form different detection performances levels for different kinds of crystal strips and same detection performances levels for same kind of crystal strips. Parameters of detection performances of crystal strips comprise energy resolution, density, size and light output, wherein different detection performances levels for crystal strips comprise one or more of parameters of detection performances of crystal strips being in different levels. Compared with a high spatial resolution PET system, the application effectively reduces manufacturing costs of a PET system without significantly reducing spatial resolution thereof. Compared with an ordinary spatial resolution PET system, it improves spatial resolution of a PET system by slightly increasing its cost, and can also provide imaging field of view with high spatial resolution in radial direction.

A positron emission tomography (PET) technique that can enhance the image resolution and system sensitivity of a clinical PET/CT scanner for imaging a whole body or a target region of a subject is provided. The system includes a detector array and a detector panel. The detector array includes an array of gamma ray detectors defining a field of view of a scanner and configured to detect at least one coincidence event. The detector panel includes an array of gamma ray detectors having a higher intrinsic spatial resolution than the detector array and positioned in closer proximity to a patient table than the detector array. The detector panel is positioned outside the field of view defined by the detector array during at least a portion of scanning by the PET system. The detector panel is configured to detect at least one coincidence event in cooperation with the detector array. The control unit is configured to control the detector array, the detector panel, and the patient bed to operate in cooperation with each other.

A circuit for receiving signals from a photodetector array arranged to detect signals generated by a crystal includes a plurality of summing circuits having weighting circuits, the summing circuits being configured to produce outputs corresponding to a total energy of the signals, a position of the signals in a first dimension of the photodetector array, a position of the signals in a second dimension of the photodetector array, and a radius of a charge distribution of the signals.

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.

A method and system for using in a Positron Emission Tomography (PET) system. The PET system comprises at least one processor and a storage. The PET system comprises an acquisition module and a processing module. The acquisition module is configured to acquire a PET data set corresponding to a target object. The acquisition module comprises a first light sensor array, a second light sensor array, and a scintillator array. The processing module is configured to determine a three-dimensional position of an incidence photon based on the PET data set. The first number of light sensors in the first light sensor array and the second number of light sensors of the second light sensor array is less than the number of scintillator of the scintillator array.

In the scatter estimation method of the present invention, Step S1 (first TOF projection data generation) and Step S4 (non-TOF scatter estimation algorithm) are performed, and Step S2 (second TOF projection data generation) and Step S3 (calculation of TOF direction distribution ratio) are performed, and Step S5 (calculation of TOF scatter projection data) is performed. A distribution ratio is obtained from the second TOF projection data measured in a scattered radiation energy window (low energy window). Since the target of distribution is non-TOF scatter projection data in a reconstruction data energy window (standard energy window), post-distribution TOF scatter projection data is obtained as approximate TOF scatter projection data in the reconstruction data energy window (standard energy window), and scatter estimation can be accurately performed.