Shenyang Neusoft Medical Systems Co., Ltd.

Shanghai Neusoft Medical Technology Co., Ltd.

Shenyang Intelligent Neuclear Medical Technology Co., Ltd.

Neusoft Medical Systems Co., Ltd.

Guodong Liang

Jian Zhao

Nan Li

Baowei Xu

Guocheng Wu

Long Yang

Xi Wang

Peng Gao

Yuqiu Zhao

Changqing Fu

Xinying Li

Jun Zhang

Donghui Han

Peng Ning

Gai Cui

Liang He

Guoxu Zhang

Rumei Zhang

Zhuxia Yin

Zhiguo Wang

The present disclosure relates to reconstructing an image. According to an embodiment of the present disclosure, identifying a plurality of first scan data sets and a second scan data set from PET scan data, wherein each of the first scan data sets corresponds to an intra-crystal Compton scattering event occurred in a plurality of crystals of a detector and includes two or more first single event data groups, and each of the first single event data groups comprises an energy value less than a preset first energy threshold, the second scan data set comprises one or more second single event data groups and each of the second single event data groups comprises an energy value exceed a preset second energy threshold; for each of the plurality of first scan data sets: searching the second scan data set for a target second single event data group which matches with the first scan data set; obtaining first coincidence event data from each of the first single event data groups in the first scan data set and the target second single event data group as coincidence event data recovered from an intra-crystal Compton scattering event corresponding to the first scan data set; reconstructing an image with the first coincidence event data and second coincidence event data which involves coincidence events corresponding to the second scan data set.

Reconstructing image

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.

Medical detectors and medical imaging devices

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.

Crystal array, detector, medical detection device and method of manufacturing crystal array

A method of calibrating time in a Positron Emission Tomography (PET) device includes obtaining original time information and energy information of a first pulse signal collected by a detecting module during a scanning process of the PET device. A detector of the PET device includes a plurality of detecting modules. The original time information of the first pulse signal includes a moment at which an amplitude of the first pulse signal begins to be greater than a threshold. The method includes determining a pulse time calibration amount corresponding to the energy information of the first pulse signal according to stored information indicative of a correspondence between the pulse time calibration amount and the energy information of each detecting module. The method includes generating calibrated time information of the first pulse signal by calibrating the original time information with the pulse time calibration amount; and reconstructing a PET image based on the generated calibrated time information.

Calibrating time in PET device

A method for determining a pair of compliance events is provided. A set of event data collected by a PET detector may be divided into N sub-sets, and each of the N sub-sets of event data may be sorted according to an occurrence time of each event included in the event data, wherein N is an integer greater than or equal to 2. A K stage heapsort may be performed on the sorted N sub-sets of event data according to the occurrence time of each event, so as to sequentially output data of each event in the sorting order, wherein K is an integer greater than or equal to 1. A time compliance determination and a space compliance determination may be performed on the sequentially-outputted event data, and a pair of compliance events may be determined if both the time compliance determination and the space compliance determination are passed.

Determining a pair of compliance events

A system and method of a PET imaging are provided. According to an example, a detector, a movement control module, a power control module and a reconstructing computer may be connected to a switch in a form of a star-shaped network topology. The detector may include M*N detector units distributed in an annular structure, each detector unit may be allocated with an IP address, M detector units are evenly distributed on each circumferential direction of the annular structure, and N detector units are evenly distributed on each axial direction of the annular structure. Each of the detector units may transmit a set of acquired data to the reconstructing computer through the switch via a network bus; and the set of data may include location information, acquiring time information and IP address. The reconstructing computer may perform a compliance process on all sets of data acquired by the detector according to the location information, acquiring time information and IP address, and reconstruct an image with the compliance data determined by the compliance process.

Positron emission tomography imaging

A method of calibrating time in a Positron Emission Computed Tomography (PET) device includes determining a rising edge slope of an electrical signal corresponding to a photon which is detected by a detector of the PET device when the PET device is used to scan a part of a subject to be examined. The method includes determining a time shift corresponding to the rising edge slope based on a correspondence between the rising edge slope and the time shift; calibrating time information of the photon based on the time shift; and reconstructing a PET image of the part of the subject to be examined based on the calibrated time information of the photon.

Methods, devices and computer-readable mediums for clock synchronization are provided. The methods include receiving a synchronizing clock in a unit clock cycle of a measuring clock, calibrating position information of a rising edge of the synchronizing clock in the unit clock cycle, determining a phase difference between the measuring clock and the synchronizing clock in the unit clock cycle based on the calibrated position information, and compensating a photon time in the unit clock cycle with the determined phase difference as a time compensation value.

Clock synchronization between time calibration boards

Methods and devices for calibrating a gain of a scintillator detector are disclosed, where a scintillation crystal of the scintillator detector includes two or more energy regions. In an example, the scintillation crystal of the scintillator detector is adopted as a radiation source for calibrating. Electric signals outputted from a rear end of the scintillator detector are collected, and actual counts of the electric signals from each of at least two energy regions of the scintillation crystal at a specified position are obtained, respectively. Then, a gain of the scintillator detector may be adjusted according to the obtained actual counts of the electric signals from the at least two energy regions.

Calibrating gain of scintillator detector

Methods, systems, and machine-readable storage mediums for determining response lines for reconstructing images are provided. An example imaging method includes: receiving single event signals in a detector module and associated with a single event, determining a crystal in the detector module and corresponding to a maximum single event signal of the single event signals, determining an actual energy weighting factor of the crystal, determining an actual depth position corresponding to the actual energy weighting factor of the crystal according to associations between depth positions of the crystal and respective reference energy weighting factors for the crystal, as an acting position in the detector module for the single event, determining a response line of a coincidence event according to respective acting positions in the detector module for two single events constituting the coincidence event, the two single events including the single event, and reconstructing an image according to the response line.

Determining response lines for image reconstruction

A method of adjusting a gain of a detector is provided in the present disclosure. According to an example, whether a gain of a photomultiplier tube in the detector meets a gain determination condition may be determined, where the gain determination condition may indicate that an absolute of a difference between the gain of the photomultiplier tube and a target gain is within a predetermined numerical range. When the gain of the photomultiplier tube does not meet the gain determination condition, a voltage of the photomultiplier tube may be adjusted, such that the gain of the photomultiplier tube meets the gain determination condition.

Adjusting gain of detector

A method and a PET apparatus are provided. According to an example of the method, a saturation indicia of a target detector may be determined through simulating emission of a &#x3b3; photon to the target detector. The target detector is any one of SiPM detectors of a PET apparatus. The saturation indicia is for designating a maximum output voltage after amplifying an output of the target detector through a VGA when one &#x3b3; photon is received by the target detector. The target VGA is a VGA corresponding to the target detector. By comparing an output voltage of the target VGA and the saturation indicia, it may determine that the target detector received a saturation event if the output voltage of the target VGA is higher than the saturation indicia. An amplifier gain of the target VGA may be adjusted until an amount of the saturation events detected by the target detector in unit time satisfies a pre-determined threshold.

Method and PET apparatus

A timing method and a timing device are disclosed. A Gray code count output may be obtained by performing a Gray code count on a basic clock. Then m number of sub-clocks may be obtained by separately performing a phase shift on a least significant bit output of the Gray code count output, where a phase difference &#x3c6; between each of the m number of sub-clocks and the least significant bit output may satisfy: &#x3c6;=n&#xd7;&#x3b1; and &#x3c6;&#x2260;90&#xb0;, 180&#xb0; may be divisible by &#x3b1; with no remainder, and n may be an integer greater than 0 and less than 180&#xb0;/&#x3b1;. If 90&#xb0; is divisible by &#x3b1; with no remainder, m=180/&#x3b1;&#x2212;2; and if 90&#xb0; is divisible by &#x3b1; with a remainder, m=180/&#x3b1;&#x2212;1. When a predetermined event occurs, a timing result of the predetermined event may be obtained according to the Gray code count output value, outputs of the m number of sub-clocks, a period of the basic clock, and the &#x3b1;.

Timing device

An apparatus for recognizing a position of a crystal in a nuclear detector, including: a silicon semiconductor detector array arranged in a crystal array in the nuclear detector, where each row/or column of silicon semiconductor detectors is configured to output a sum of voltages outputted by the silicon semiconductor detectors in the row/or column at a row/or column signal output end; row signal comparing modules, one to one correspondingly connected to each row signal output end and configured to obtain a row comparison result for each row of silicon semiconductor detectors; column signal comparing modules, one to one correspondingly connected to each column signal output end and configured to obtain a column comparison result for each column of silicon semiconductor detectors; and a crystal position recognizing module configured to recognize a position of a crystal hit by a photon according to each row comparison result and each column comparison result.

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Shenyang, China

Guodong Liang