The present disclosure provides devices, systems, and methods for time correction. The device may include a first time measurement component configured to measure a receiving time of a valid signal; a correction component configured to collect correction information for correcting the receiving time of the valid signal; and a processing device configured to determine a corrected receiving time of the valid signal by correcting the receiving time of the valid signal based on the correction information.

The present invention relates to a method and a device for monitoring body parts of a patient simultaneously by means of high-resolution and high-sensitivity detection techniques which detect radiation emitted by a tracer. It is an object of the present invention a device for the enhanced determination of a fine location of at least one tracer within a body part of a patient which comprises a first pair of high-resolution detectors opposing detectors, and a second pair of high-sensitivity detectors and movable opposing detectors, and the device being configured to determine based on signals from the first pair of opposing detectors, position the second pair of opposing detectors based on the coarse location, and determining a fine location of the tracer based on signals from the second pair of opposing detectors, allowing to determine the location of a tracer with high spatial resolution and high sensitivity.

A device for the detection of gamma rays used primarily in a PET scanner is based on a scintillator heterostructure combining the high stopping power of scintillators commonly used in PET scanners (such as L(Y)SO, BGO, etc.) and very fast scintillators based on polymers loaded with fast emitting dyes or nanocrystals, or thin layers of nanocrystals or multiple quantum well structures. The particular arrangement of this detector module allows combining all the important features of a high-performance Time-of-Flight PET (TOFPET) detector module, i.e., a high photoelectric detection efficiency for the gamma rays, a precise 3D information (including the depth of interaction DOI) of the gamma ray conversion in the module, and good energy resolution.

A method and system for calibrating a PET scanner are described. The PET scanner may have a field of view (FOV) and multiple detector rings. A detector ring may have multiple detector units. A line of response (LOR) connecting a first detector unit and a second detector unit of the PET scanner may be determined. The LOR may correlate to coincidence events resulting from annihilation of positrons emitted by a radiation source. A first time of flight (TOF) of the LOR may be calculated based on the coincidence events. The position of the radiation source may be determined. A second TOF of the LOR may be calculated based on the position of the radiation source. A time offset may be calculated based on the first TOF and the second TOF. The first detector unit and the second detector unit may be calibrated based on the time offset.

According to one embodiment, a converter array includes a first substrate, multiple sets of a plurality of analog-digital converters and a switch. The multiple sets are arranged on the first substrate in array. The switch is configured to switch a connection relationship between the plurality of analog-digital converters to process signals from photodiodes smaller in number than the analog-digital converters.

A radiation detector head assembly includes a detector column. The detector column includes a detector having a first surface and a second surface opposite the first surface. The detector column also includes a first collimator disposed over the first surface of the detector configured for use during imaging scans involving radiation in a first energy range. The detector column further includes a second collimator disposed over the second surface of the detector configured for use during imaging scans involving radiation in a second energy range different from the first energy range.

The disclosure relates to a system and method for evaluating and calibrating detector in a scanner, further evaluating and calibrating time information detected by at least one time-to-digital convertor.

Techniques for counting respective photons having energy levels within at least a first energy window and a second energy window, where the first energy window is lower than the second energy window, are presented. The techniques include: receiving a first indication of a first photon detection, the first photon detection being of a photon having an energy of at least a lower end of the first energy window; receiving a second indication of a second photon detection, the second photon detection being of a photon having an energy of at least a lower end of the second energy window; within a predetermined time interval of the receiving the first indication, communicating locally the second indication to counter logic for the first energy window, where a counter for the first energy window is not incremented; and incrementing a counter for an energy window higher than the first energy window.

The present disclosure is related to a system. The system may include a gantry, a detector assembly including a plurality of detector modules arranged on the gantry, and/or a cooling assembly configured to cool the detector assemble. Each of the plurality of detector modules may include a crystal array configured to detect radiation rays, and a shielding component configured to shield the crystal array from an electromagnetic interference. The cooling assembly may include a plurality of cooling components. Each of the plurality of cooling components may be embedded in a corresponding detector module of the plurality of detector modules.

The present disclosure provides a gamma ray imaging device and an imaging method, where the imaging device includes a plurality of separate detectors. The plurality of separate detectors are provided at an appropriate spatial position, in an appropriate arrangement manner and are of an appropriate detector material, such that when rays emitted from different positions in an imaging area reach at least one of the plurality of separate detectors, at least one of the thicknesses of the detectors, the materials of the detectors, and the numbers of the detectors though which the rays pass are different, thereby achieving the effect of determining the directions of rays.