Abstract: A PET imaging system, with parallel detector rings sharing a common axis (e.g., rings with one or more detector elements in the axial direction and two or more detector elements in the transaxial direction), may have an adaptive axial and/or transaxial FOV by employing a sparse detector configuration and adapting the size of axial gaps between rings and/or the size of transaxial gaps between detector elements in each ring. The axial FOV may be dynamic, enabling PET data acquisition in multiple modes (e.g., “retracted” with detector rings in a compact configuration, and “extended” with detector rings extended for longer axial FOV). The transaxial FOV may be dynamic, enabling an adaptive detector ring diameter for different body part contours. The sparse detector ring configurations may be used to extend the scanner axial and/or transaxial FOV, or retain the current system's FOV with half the number of (or otherwise fewer) detector elements.

Abstract: The present disclosure relates to reconstructing an image.

Abstract: One example device comprises a plurality of emitters including at least a first emitter and a second emitter. The first emitter emits light that illuminates a first portion of a field-of-view (FOV) of the device. The second emitter emits light that illuminates a second portion of the FOV. The device also comprises a controller that obtains a scan of the FOV. The controller causes each emitter of the plurality of emitters to emit a respective light pulse during an emission time period associated with the scan. The controller causes the first emitter to emit a first-emitter light pulse at a first-emitter time offset from a start time of the emission time period. The controller causes the second emitter to emit a second-emitter light pulse at a second-emitter time offset from the start time of the emission time period.

Abstract: A display device includes a display panel including a plurality of pixels, a data driver configured to provide data signals to the plurality of pixels, a scan driver configured to provide scan signals to the plurality of pixels, and a controller configured to control the data driver and the scan driver. The controller includes a volatile age memory configured to store accumulated degradation amounts for the plurality of pixels, and an internal age memory configured to store backup accumulated degradation amounts generated based on the accumulated degradation amounts. The controller is further configured to compensate input image data by selectively using the accumulated degradation amounts of the volatile age memory or the backup accumulated degradation amounts of the internal age memory.

Abstract: A computer-implemented method for provision of a correction algorithm for an x-ray image that was recorded with an x-ray source emitting an x-ray radiation field, a filter facility spatially modulating an x-ray radiation dose, and an x-ray detector is provided. The correction algorithm includes a trained first processing function that, from first input data that includes at least one first physical parameter describing the x-ray radiation field and/or the measurement and at least one second physical parameter describing the spatial modulation of the filter facility, determines first output data. The first output data includes a mask for brightness compensation with regard to the spatial modulation of the filter facility in the x-ray image. The method includes providing first training data, providing an autoencoder for masks, and training of the autoencoder using the first training data. The method also includes determining an assignment rule, and providing the trained first processing function.

Abstract: A processing system includes a digital processing unit programmable as a function of a firmware stored to a non-volatile memory and a resource connected to the digital processing unit via a communication system. The processing system also includes a time reference circuit including a first digital counter circuit to generate, in response to a clock signal, a system time signal including a plurality of bits indicative of a time tick-count, and a time base distribution circuit to generate a time base signal by selecting a subset of the bits of the system time signal, wherein the time base signal is provided to the resource. The resource detects a given event, stores the time base signal to a register in response to the event, and signals the event to the digital processing unit. The digital processing unit reads, via the communication system, the time base signal from the register.

Abstract: A method for detecting potential faults in a cooling system that cools a detector electronic assembly (DEA) of a positron emission tomography (PET) imaging system having a plurality of PET detector rings each including a plurality of PET detectors having an associated DEA. The method includes verifying continuity of coolant lines in a coolant flow path of a DEA and calculating a flow rate through a coolant flow path of a DEA. Selected circuit board temperature sensors are used to detect temperature values that serve as surrogates for temperature change of a coolant. Further, the selected temperature sensors are located on hardware that is replicated on different points or locations on the flow path such that the temperature sensors have similar performance characteristics and are of like kind.

Abstract: Multiple interactions, such as Compton scattering, inside a PET detector are used to predict an incident photon's direction for identifying true coincidence events versus scatter/random coincidence events by creating a cone shaped shell projection defining a range of possible flight directions for the incident photon. The disclosed techniques can be used as prior information to improve the image reconstruction process. The disclosed techniques can be implemented in a LYSO/SiPM-based layer stacked detector, which can precisely register multiple interactions' 3D position.

Abstract: The disclosure relates to a system and method for image reconstruction. The method may include the steps of: obtaining raw data corresponding to radiation rays within a volume, determining a radiation ray passing a plurality of voxels, grouping the voxels into a plurality of subsets such that at least some subset of voxels are sequentially loaded into a memory, and performing a calculation relating to the sequentially loaded voxels. The radiation ray may be determined based on the raw data. The calculation may be performed by a plurality of processing threads in a parallel hardware architecture. A processing thread may correspond to a subset of voxels.

Abstract: The present disclosure relates to a PET detector and a PET frame. The PET detector may include a plurality of detector modules and a plurality of installing modules configured to install the plurality of detector modules. The plurality of installing modules may be coupled together to form a detector ring. The PET frame may include a detector stabilizing cylinder configured to stabilize a detector and a fixing support configured to support the detector stabilizing cylinder. The detector stabilizing cylinder may be rotatably fixed on the fixing support.

Abstract: A system, device and method facilitate accurate detection of gunshot events through spectrum analysis of impulse signals and/or evaluating impulse signal exponential decay amplitude and time values. In various embodiments, the device and system employ an acoustic sensor, one or more high-pass and low-pass filters, a threshold detector, a differentiator, a decay waveform shape generator, one or more comparators and one or more timers to facilitate detection of gunshot events and/or components of gunshot events.

Abstract: 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.

Abstract: A non-transitory computer-readable medium stores instructions readable and executable by a workstation (18) including at least one electronic processor (20) to perform an image reconstruction method (100) to reconstruct list mode data acquired over a frame acquisition time using a plurality of radiation detectors (17) in which the events of the list mode data is timestamped.

Abstract: 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.

Abstract: The invention provides a novel arrangement of photon sensors on a scintillation-crystal based gamma-ray detector that takes advantage of total internal reflection of scintillation light within the scintillation detector substrate. The present invention provides improved spatial resolution including depth-of-interaction (DOI) resolution while preserving energy resolution and detection efficiency, which is especially useful in small-animal or human positron emission tomography (PET) or other techniques that depend on high-energy gamma-ray detection. Moreover, the new geometry helps reduce the total number of readout channels required and eliminates the need to do complicated and repetitive cutting and polishing operations to form pixelated crystal arrays as is the standard in current PET detector modules.

Abstract: Systems and methods are provided for evaluating tissue for abnormal glucose uptake within a region of interest within a patient. A PET scanner obtains PET imagery including the region of interest and at least part of the liver. An SUV calculator calculates a first set of SUVs representing the region of interest and a second set SUVs representing the liver from the set of at least one PET image. A standardization component calculates a correction value as a function of the second set of SUVs and applies the correction value to either a decision threshold associated with the region of interest or the first set of SUVs. A diagnosis component compares the first set of SUVs to the decision threshold to determine if the glucose uptake within the region of interest is abnormal. A display provides the determination to a user.

Abstract: A method of estimating energy-based scatter content in PET list-mode data is provided.

Abstract: A scintillator assembly including an entrance surface for receiving charged particles into the scintillator assembly, the charged particles including first charged particles at a first energy level and second charged particles at a second energy level. A first scintillator structure configured for receiving the first charged particles and generating a corresponding first signal formed of first photons with a first wavelength of ?1, a second scintillator structure configured for receiving the second charged particles and generating a corresponding second signal of second photons with a second wavelength of ?2, and an emitting surface for egress of a combined signal from the scintillator assembly, the combined signal including the first and second photons, and at least one beam splitter for receiving the combined signal and separating the combined signal to first and second photons.

Abstract: Medical detectors and medical imaging devices are provided. In one aspect, a medical detector includes: a photoelectric conversion device, a first crystal array layer disposed over the photoelectric conversion device, and a second crystal array layer disposed over the first crystal layer. The first crystal array layer includes a plurality of first scintillation crystals arranged in a first crystal array, and a first coupling medium being filled between every adjacent two of the first scintillation crystals. The second crystal array layer includes a plurality of second scintillation crystals arranged in a second crystal array, and a second coupling medium being filled between every adjacent two of the second scintillation crystals. A light transmittance of the second coupling medium is different from a light transmittance of the first coupling medium.

Abstract: The disclosed scanner for detecting a decay time of light emitted by a luminescent material has a control unit operable to adapt the drive current, or the value of the drive voltage, powering its light source to accordingly adapt the intensity of excitation light delivered to the luminescent material so that its high sensitivity light sensor can reliably measure the luminescence light emitted in response to the excitation light, and thus accurately determine a corresponding decay time value.

Abstract: The present disclosure relates to a PET detector and a PET frame. The PET detector may include a plurality of detector modules and a plurality of installing modules configured to install the plurality of detector modules. The plurality of installing modules may be coupled together to form a detector ring. The PET frame may include a detector stabilizing cylinder configured to stabilize a detector and a fixing support configured to support the detector stabilizing cylinder. The detector stabilizing cylinder may be rotatably fixed on the fixing support.

Abstract: A Time-Resolved PET imaging system for producing an event-by-event, real-time, high resolution, three-dimensional positron emission tomographic images without performing sinogram formation or image reconstruction. The third dimension is provided by measuring the ?T between the arrival times of gamma rays from a positron event being detected by two cooperating detectors. In order to determine the location of a positron event along the lines of response, the measurement includes a fast scintillator, constant fraction discriminator and the digital intervalometer. The arrival time of each photon in the annihilation process is recorded with respect to a clock frequency with picosecond resolution. This approach requires significantly fewer positron events, thus requiring fewer detectors, thereby resulting in an gamma event-by-gamma event, real-time TPET imaging system that is more efficient and more economical to produce than conventional PET systems.

Abstract: A system, device and method facilitate accurate detection of gunshot events through spectrum analysis of impulse signals and/or evaluating impulse signal exponential decay amplitude and time values. In various embodiments, the device and system employ an acoustic sensor, one or more high-pass and low-pass filters, a threshold detector, a differentiator, a decay waveform shape generator, one or more comparators and one or more timers to facilitate detection of gunshot events and/or components of gunshot events.

Abstract: Methods for simulating, and correcting for, doubly scattered annihilation gamma-ray photons in both time-of-flight (TOF) and non-TOF positron emission tomography scan data are disclosed.

Abstract: A time correction device for a PET system comprises a detector ring, a ring-shaped prosthesis, and detection, data acquisition, data coincidence, time shift calculation, data correction application modules. Center of the ring-shaped prosthesis overlaps with axial and radial center of the detector ring. The detection module is located in ring-shaped prosthesis. Center of the detection module is at the center of the ring-shaped prosthesis. The data acquisition module comprises data gathering and energy filtering modules connected to each other. The data gathering module comprises detectors and the detection module. The energy filtering module connects to the data gathering module receiving single-event time information. The data coincidence module is connects to the energy filtering module receiving the single-event time information. Time shift calculation module connects to the data coincidence module providing a shift value of the detectors.

Abstract: A radiation imaging apparatus comprises a sensor unit including two sensor boards stacked together, a base supporting the sensor unit, an electrical component on an opposite side to the sensor unit relative to the base, and a heat insulation member including a portion located between the electrical component and the sensor unit. A heat conductivity of the heat insulation member is lower than a heat conductivity of the base.

Abstract: A scintillator material includes a matrix phase and scintillator parts dispersed in the matrix phase. The scintillator parts contain fine particles of single crystal. According to the above aspect, since the scintillator parts containing the fine particles of single crystal are dispersed in the matrix phase, it is possible to reduce an influence from an environment.

Abstract: The invention concerns a detecting apparatus (12) comprising:—at least two sensors (24, 26, 28), with at least one sensor (24) being an ultrasound transducer adapted to produce ultrasound waves, and—a positioning device (16) defining several compartments (22), each compartment (22) being adapted to hold a sensor (24, 26, 28) and each compartment (22) being located at predetermined location, the positioning device (16) comprising a holder adapted to be fixed on the skull of a subject, the positioning device (16) being adapted to be maintained on the head of the subject using the holder.

Abstract: A positron emission tomography (PET) assembly includes an annular housing and an annular scintillator disposed within the annular housing. The annular scintillator includes an annular, substantially continuous crystal scintillator tube configured to absorb ionizing radiation and to emit light energy. A plurality of photo detectors are annularly disposed around the annular scintillator within the annular housing and configured to detect the emitted light energy.

Abstract: A detector module system for positron emission tomography including a plurality of gamma ray detector modules. Each pair of one detector module and one interconnection element includes mutually engaging locking means for releasably connecting the detector module to the interconnection element. Further each interconnection element includes locking means for releasably connecting at least two detector modules to said interconnection element. Further each of said gamma ray detector modules includes a sensor adapted to detect gamma radiation occurring from short-lived radionuclides radiating from a body and to generate a radiation output corresponding to the detected gamma radiation, and the detector module system comprises a processing circuitry adapted to receive said radiation output from each of the gamma ray detector modules and to generate a resulting radiation representation for the positron emission tomography event, based on the received radiation output.

Abstract: A variable PET apparatus allows structural changes of detector modules in transversal and longitudinal directions to correspond to various imaging purposes and a cross-sectional diameter of a subject while maintaining an arrangement of the detector modules to be close to a true circle. The variable PET apparatus includes: a gantry having an opening on a longitudinal axis; and detector modules supported on the gantry and arranged a predetermined distance apart from each other such that a detection ring is configured with a diameter in a circumferential direction, wherein the gantry is driven by a gantry drive member, and the detector modules are driven by a detector module drive member. According to the present invention, structural changes of the detector modules in the PET apparatus is possible to correspond to a cross-sectional diameter of a subject without additional devices, thereby improving the spatial resolution and sensitivity.

Abstract: Detector heads in a gantry of a medical imaging apparatus are pivotally-coupled to mounting rails oriented axially about the gantry's axial centerline. Radial alignment blocks facilitate alignment and fixation of detector faces circumferentially transverse and normal to a radius projecting from the gantry's axial centerline. A column of detector heads on a common rail are separated by axial stop blocks, for precise axial separation. Abutting detector heads on a common mounting rail are slaved to another previously transverse-aligned detector through a common, shared radial alignment block. Plural, stacked gantry backplanes are fabricated simultaneously, assuring common circumferential and radial co-registration of plural mounting rails relative to the axial centerline of the gantry. Adjustable orientation of the detector heads compensates for tolerance stack up during final assembly of the gantry, so that the detector heads are mutually aligned in a uniform grid of axial columns and circumferential rows.

Abstract: A crystal array, a detector, a medical detection device and a method for manufacturing a crystal array are provided. The crystal array includes a plurality of crystals arranged in an array, each of the crystals having a light incident surface, a light exit surface, and a connection surface connecting the light incident surface to the light exit surface, where the connection surface of at least one of two adjacent crystals includes a rough surface and a smooth surface connected to the rough surface, and the rough surface and the smooth surface are arranged along a length direction of the crystal.

Abstract: An optical system may include a substrate and a plurality of silicon photomultipliers (SiPMs) monolithically integrated with the substrate. Each SiPM may include a plurality of single photon avalanche diodes (SPADs). The optical system also includes an aperture array having a plurality of apertures. The plurality of SiPMs and the aperture array are aligned so as to define a plurality of receiver channels. Each receiver channel includes a respective SiPM of the plurality of SiPMs optically coupled to a respective aperture of the plurality of apertures.

Abstract: A positron emission tomography scanner includes a plurality of gamma-ray detector rings that form a bore through which an imaging subject is translated, each of the plurality of gamma-ray detector rings being in a first axial position, and processing circuitry configured to receive attenuation data associated with a plurality of transaxial slices of the imaging subject, determine a second axial position of each of the plurality of gamma-ray detector rings based on the received attenuation data, and adjust a position of each of the plurality of gamma-ray detector rings from the first axial position to the second axial position. The processing circuitry may further be configured to calculate an attenuation metric based on the received attenuation data, and determine the second axial position such that the attenuation metric calculated for each pair of adjacent gamma-ray detector rings is equal.

Abstract: Systems and methods include acquisition of data representing true coincidences and scatter coincidences detected by the plurality of detectors, allocation of the data into respective ones of a plurality of energy ranges, determination of a baseline response associated with each of a subset of the plurality of energy ranges, generation of data representing expected true coincidences associated with each of the subset of the plurality of energy ranges based on the data allocated to each of the subset of the plurality of energy ranges and the baseline response associated with each of the subset of the plurality of energy ranges, determination of a raw scatter estimate based on the data representing expected true coincidences associated with each of the subset of the plurality of energy ranges and the data allocated to each of the subset of the plurality of energy ranges, and reconstruction of an image based on the raw scatter estimate and the data representing true coincidences and scatter coincidences.

Abstract: A method for determining a correction profile of an imaging device may include obtaining first data relating to the imaging device; comparing the first data and a first condition; obtaining, based on the comparison, a first correction profile relating to the imaging device; and calibrating, based on the first correction profile, the imaging device.

Abstract: A method of PET image reconstruction is provided that includes obtaining intra-patient tissue activity distribution and photon attenuation map data using a PET/MRI scanner, and implementing a Maximum Likelihood Expectation Maximization (MLEM) method in conjunction with a specific set of latent random variables, using an appropriately programmed computer and graphics processing unit, wherein the set of latent random variables comprises the numbers of photon pairs emitted from an electron-positron annihilation inside a voxel that arrive into two given voxels along a Line of Response (LOR), where the set of latent random variables results in a separable joint emission activity and a photon attenuation distribution likelihood function.

Abstract: A positron emission tomography (PET) detector array includes an enclosing radiation detector array (10) comprising radiation detector elements (14, 16) effective for detecting 511 keV radiation emanating from inside the radiation detector array. The radiation detector pixels of the cylindrical radiation detector array include both higher speed radiation detector elements (14) and lower speed radiation detector elements (16). The lower speed radiation detector pixels have a temporal resolution that is coarser than a temporal resolution of the higher speed radiation detector pixels.

Abstract: A system is provided that includes at least one detector and a processing unit. The at least one detector is configured to acquire imaging information. The processing unit is operably coupled to the at least one detector, and is configured to acquire the imaging information from the at least one detector. The processing unit is configured to acquire patient scanning information for an imaging operation, determine a target activity based on the patient scanning information, determine a target time for performing the imaging operation corresponding to the target activity, perform the imaging operation at the target time to acquire targeted imaging information; and reconstruct an image using the targeted imaging information.

Abstract: A visual test system for a secondary generation or decomposition of a hydrate includes a hydrate conveying device, a computerized tomography (CT) imaging device, a temperature control device, a pressure control device and a flow control device. The hydrate conveying device includes an annular pipeline structure composed of a plurality of straight pipeline sections and a plurality of curved pipeline sections. The straight pipeline section is able to rotate around an axis thereof under the drive of a pipeline driving device. The CT imaging device is used to perform a three-dimensional (3D) detection inside the pipeline, and includes a turntable, a ray source and a detector. The ray source is able to rotate under the drive of the turntable driving device. The temperature control device, the pressure control device and the flow control device are used to control a gas-liquid mixture's temperature, pressure and flow rate, respectively.

Abstract: A scintillator assembly including an entrance surface for receiving charged particles into the scintillator assembly, the charged particles including first charged particles at a first energy level and second charged particles at a second energy level. A first scintillator structure configured for receiving the first charged particles and generating a corresponding first signal formed of first photons with a first wavelength of ?1, a second scintillator structure configured for receiving the second charged particles and generating a corresponding second signal of second photons with a second wavelength of ?2, and an emitting surface for egress of a combined signal from the scintillator assembly, the combined signal including the first and second photons, and at least one beam splitter for receiving the combined signal and separating the combined signal to first and second photons.

Abstract: In some aspects, the techniques described herein relate to systems, methods, and computer readable media for data pre-processing for stereo-temporal image sequences to improve three-dimensional data reconstruction. In some aspects, the techniques described herein relate to systems, methods, and computer readable media for improved correspondence refinement for image areas affected by oversaturation. In some aspects, the techniques described herein relate to systems, methods, and computer readable media configured to fill missing correspondences to improve three-dimensional (3-D) reconstruction. The techniques include identifying image points without correspondences, using existing correspondences and/or other information to generate approximated correspondences, and cross-checking the approximated correspondences to determine whether the approximated correspondences should be used for the image processing.

Abstract: Disclosed is a PET detector assembly in a combined PET/CT scanner system having a backplane structure for supporting two or more PET detector rings that provides substantially balanced load on the gantry backplane while accommodating the varying number of PET detector rings between short axial PET FOV system as well as long axial PET FOV system.

Abstract: There are provided a radiation imaging system and a transmission device capable of reducing a user's standby time compared to a case where a tomographic image is transmitted. A console acquires a plurality of projection images obtained by tomosynthesis imaging, generates a plurality of tomographic images by reconstruction using the plurality of projection images, synthesizes a 2-dimensional image based on the plurality of tomographic images, transmits the synthesized 2-dimensional image to an image interpretation support device, and transmits the plurality of projection images to the image interpretation support apparatus.

Abstract: According to one embodiment, an X-ray computed tomography apparatus includes an X-ray tube and an X-ray detector. The X-ray tube generates X-rays. The X-ray detector includes a first detection area detecting the X-rays and a second detection area detecting the X-rays. The first detection area includes a first scintillator having a first fluorescence decay time, the second detection area includes a second scintillator having a second fluorescence decay time shorter than the first fluorescence decay time. The second detection area is arranged at both ends of the first detection area with respect to a channel direction.

Abstract: A scintillation crystal can include Ln(1-y)REyX3, wherein Ln represents a rare earth element, RE represents a different rare earth element, y has a value in a range of 0 to 1, and X represents a halogen. In an embodiment, RE is Ce, and the scintillation crystal is doped with Sr, Ba, or a mixture thereof at a concentration of at least approximately 0.0002 wt. %. In another embodiment, the scintillation crystal can have unexpectedly improved linearity and unexpectedly improved energy resolution properties. In a further embodiment, a radiation detection system can include the scintillation crystal, a photosensor, and an electronics device. Such a radiation detection system can be useful in a variety of radiation imaging applications.

Abstract: The complex comprising one or more of the compound represented by general formula: RPbn1Xm1 (wherein R is a cation represented by R1NH3+ (wherein R1 represents a univalent substituted or unsubstituted hydrocarbon group), or the following formula: (wherein R2 represents a hydrogen atom, or a univalent substituted or unsubstituted hydrocarbon group); X is the same or different, and each represents a halogen atom; n1 is 0.8 to 1.2; and m1 is 2.8 to 3.2, or the compound represented by general formula: R2Pbn2Xm2 wherein R and X are as defined above; n2 is 2.8 to 3.2; and m2 is 7.7 to 8.3; and one or more dimethylformamide molecules is capable of decreasing the stirring time upon dissolution in an organic solvent such as DMSO, as well as decreasing the hysteresis and improving the solar cell characteristics (in particular, photoelectric conversion efficiency) when the complex is applied to a perovskite layer.

Abstract: Provided is a real-time detector of a Bragg peak, comprising: an emitter configured to emit a particle beam toward a target region in a first direction, thereby creating emission of electromagnetic radiation in the target region; a first detection module comprising a stack of first scintillators and first photosensors respectively connected to the first scintillators and configured to detect the electromagnetic radiation and convert into a first signal; a second detection module comprising a stack of second scintillators and second photosensors respectively connected to the second scintillators and configured to detect the electromagnetic radiation and convert into a second signal; and a coincidence detection circuit configured to determine an end point of the particle beam with respect to the first direction based on the first signal and the second signal.

Abstract: A method for synchronizing list-mode data of single events in a PET imaging includes: acquiring list-mode data of single events of each independent detector module, calculating a probability density of time intervals between occurrences of single events in detector module and setting initial parameters, determining detection starting time difference of each detector module with iterative peak searching and graded time window, and performing synchronization correction and coincidence discrimination on the single event data in each detector module based on the detection starting time difference. A system for synchronizing list-mode data of single events in a PET imaging includes: a data acquisition and frequency difference compensation module, an initial parameter setting module, a coarse time scale coincidence module, a fine time scale coincidence module and a data synchronization correction and coincidence discrimination module.