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 photoelectric converter includes a silicon photomultiplier array and a light guide coupled to the silicon photomultiplier array. The silicon photomultiplier array is generated by splicing i×j silicon photomultipliers on a horizontal plane, where both i and j are integers greater than or equal to 2. A detector includes a scintillation crystal, an electronic system, a light guide and a silicon photomultiplier. A scanning device includes a detection apparatus and a rack, the detection apparatus includes a detector, and the detector includes the photoelectric converter.

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.

Abstract: Provided is a flat-plate PET imaging device with a window (11), comprising: a first flat plate (10) formed of a plurality of PET detectors arranged in sequence into a plate shape and provided with at least one window (11); a second flat plate (20) formed of a plurality of PET detectors arranged in sequence into a plate shape and parallel to the first flat plate (10) and the second flat plate (20) are fixed. By arranging a window (11) on the flat-plate PET, a space is provided for other operations, such as radiotherapy, while ensuing the real-time positioning and scanning effects, thereby actually achieving real-time diagnosis as well as positioning and navigation without affecting the therapeutic procedure.

Abstract: A method for real-time processing of a pulse pile-up event comprises the following steps of: generating a fitted baseline value lookup table and a fitted energy value lookup table for a pulse falling edge, using a multi-voltage threshold sampling method to identify piled-up pulses and trigger a procedure of processing pulse signals; and using pulse priori information and acquired pulse information to acquire information of an incorrectly sampled portion due to a pulse pile-up by looking up in the tables, so as to recover information of the pile-up pulses in real time. First, in the disclosure the multi-voltage threshold sampling method is proposed to identify pile-up pulses at a high count rate and trigger a procedure of processing pulse signals. Next, pulse priori information and acquired pulse information are used to acquire information of an incorrectly sampled portion due to a pulse pile-up by looking up in the tables, to recover information of the piled-up pulses in real time.

Abstract: An individualized imaging method, comprising the following steps: scanning an imaging subject mold; conducting calibration, rectification and optimization on the imaging system according to the information obtained after mold imaging: scanning the imaging subject with the calibrated, rectified and optimized imaging system; optimizing information obtained by scanning the imaging subject and the mold thereof to obtain higher quality imaging results and data analysis result; and applying the higher quality imaging results and data analysis results to optimize the mold for use in the next imaging.

Abstract: A method for digitalizing a scintillation pulse may include: S1, acquiring a pulse database outputted by a detector irradiated by rays of different energy; S2, sampling and 5 quantizing each of pulses in the pulse database obtained in S1 to acquire complete energy information comprised in the pulse, S3, undersampling and quantizing each of the pulses in the pulse database obtained in step S1, and estimating or fitting energy information by using pulse prior information; S4, with the energy information obtained in S2 as a standard, determining a mapping relationship between 10 the energy information obtained by a prior information-based undersampling pulse energy acquisition method and the energy information obtained by the method of S2; and S5 correcting the energy information obtained by the prior information-based undersampling pulse energy acquisition method by using the energy mapping relationship obtained in S4.

Abstract: A time label combination method, comprising the steps: collecting data acquisition system digital measurement values and establishing a database for the measured values; identifying atomic time label quantities and shape fluctuation statistics; estimating a covariance matrix of each atomic time label; according to the least squares criterion, giving the time label combination. Also provided is a time label combination system, comprising a low-dose pre-acquisition data module, a digital identification module, a quantitative variance calculation module, and a time label combination parameter calculation module. By means of using the described time label combination method and system, system and resolution is effective increased, and the invention is particularly suitable for nuclear instrument time acquisition.

Abstract: A combined scintillation crystal includes: at least one scintillation crystal A module and a scintillation crystal B module. The scintillation crystal A module and the scintillation crystal B module are scintillation crystal modules with different performances. The scintillation crystal A module comprises at least one scintillation crystal A, and the scintillation crystal B module comprises at least one scintillation crystal B. The sensitivity of the scintillation crystal A is lower than the sensitivity of the scintillation crystal B, and the light output ability of the scintillation crystal A is higher than the light output ability of the scintillation crystal B. The scintillation crystal B module includes a ray incidence plane for receiving rays, and the at least one scintillation crystal module A is arranged at the outer side of the ray incidence plane of the scintillation crystal B module.

Abstract: A channel multiplexing method for reading array detector signals includes: dividing array detectors into M groups, at least two detectors being in each group; array coding the read channel to read M row signals and N column signals, which means when a signal is outputted at the detector in row a, column b, the signals of row a and column b are outputted correspondingly; connecting the readout signals of-the row and the column to different positions of two transmission lines respectively; determining the source row number and column number of the signal on the basis of the time difference between the time of signal reaching two ends of the transmission line, and marking the source detector from which the signal is generated on the basis of two time differences of the row signal and the column signal.

Abstract: A method for extracting scintillation pulse information includes followed steps: 1. obtaining a peak value of the scintillation pulse in a certain energy spectrum, and setting at least three threshold voltages according to the peak value; 2. determining the time when the scintillation pulse passes through the each threshold voltage, wherein each time value and its corresponding threshold voltage form a sampling point; 3. selecting multiple sampling points as sampling points for reconstructing and reconstructing pulse waveform; 4. obtaining the data of original scintillation pulse by using reconstructed pulse waveform. A device for extracting scintillation pulse information includes a threshold voltage setting module (100), a time sampling module (200), a pulse reconstruction module (300) and an information acquiring module (400).

Abstract: A PET detection structure with application adaptability includes: at least two detector blocks and a detection ring for disposing the detector blocks. The at least two detector blocks are placed on the detection ring and surround a detected object in a manner of encirclement. The performance of each detector block includes inherent spatial resolution, time behavior, energy resolution, detection efficiency and maximum counting rate. The performance of the detector blocks are divided into a plurality of performance levels, and the performance level of one performance of at least one detector block of the at least two detector blocks is higher than the performance rate of the same performance of the other detector blocks.

Abstract: A crystal-array module includes a number of unit crystal strips. The three-dimensional shape of the crystal-array module is a frustum or a combination of a right quadrangular prism and the frustum. The frustrum includes a first bottom face coupled with a photoelectric device and a first top face opposed to the first bottom face. The area of the first bottom face is smaller than that of the first top face. A fabrication method of the crystal-array module includes joining cut unit crystal strips or cut unit crystal strip arrays together.

Abstract: A crystal-array module includes a number of unit crystal strips. The three-dimensional shape of the crystal-array module is a frustum or a combination of a right quadrangular prism and the frustum. The frustrum includes a first bottom face coupled with a photoelectric device and a first top face opposed to the first bottom face. The area of the first bottom face is smaller than that of the first top face. A fabrication method of the crystal-array module includes joining cut unit crystal strips or cut unit crystal strip arrays together.

Abstract: A threshold correction method is for a multi-voltage threshold sampling digitization device. The method includes: generating a triangular wave, and measuring the slope k1 of the rising edge part and the slope k2 of the falling edge part of the waveform of the triangular wave and the peak value amplitude Vpeak thereof, the width DOT of the part of the pulse higher than an actual working threshold Vt being represented as DOT(Vt)=(Vpeak?Vt)/k1?(Vpeak?Vt)/k2; setting n groups of threshold pairs; calculating a threshold under an actual working state using the measured pulse width DOT according to a formula; and establishing a threshold correction function according to a corresponding relationship between actual working state thresholds and reference voltages set practically, and then correcting a set threshold according to the function.

Abstract: A threshold correction method is for a multi-voltage threshold sampling digitization device. The method includes: generating a triangular wave, and measuring the slope k1 of the rising edge part and the slope k2 of the falling edge part of the waveform of the triangular wave and the peak value amplitude Vpeak thereof, the width DOT of the part of the pulse higher than an actual working threshold Vt being represented as DOT(Vt)=(Vpeak?Vt)/k1?(Vpeak?Vt)/k2; setting n groups of threshold pairs; calculating a threshold under an actual working state using the measured pulse width DOT according to a formula; and establishing a threshold correction function according to a corresponding relationship between actual working state thresholds and reference voltages set practically, and then correcting a set threshold according to the function.

Abstract: A PET detection structure with application adaptability includes: at least two detector blocks and a detection ring for disposing the detector blocks. The at least two detector blocks are placed on the detection ring and surround a detected object in a manner of encirclement. The performance of each detector block includes inherent spatial resolution, time behavior, energy resolution, detection efficiency and maximum counting rate. The performance of the detector blocks are divided into a plurality of performance levels, and the performance level of one performance of at least one detector block of the at least two detector blocks is higher than the performance rate of the same performance of the other detector blocks.

Abstract: A multilayer scintillation crystal (1) comprises n layers of array scintillation crystals and m layers of continuous scintillation crystals which have uncut inner parts, both n and m being integers greater than or equal to 1 and a sum of n and m being smaller than or equal to 10. The array scintillation crystals are formed by strip-type scintillation crystals arranged along the width and length directions, the array scintillation crystals and the continuous scintillation crystals are sequentially coupled along the height direction of the strip-type scintillation crystals to form the multilayer scintillation crystal (1), and the continuous scintillation crystals are located at the bottom of the multilayer scintillation crystal (1).

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 detection module, calculating a probability density of time intervals between occurrences of single events in detection module and setting initial parameters, determining detection starting time difference of each detection module with iterative peak searching and graded time window, and performing synchronization correction and coincidence discrimination on the single event data in each detection 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.

Abstract: A positron emission tomography method and a device with application adaptability. The method includes: step 1, scanning a tested object for obtaining initial activity information of the tested object; step 2, programming and adjusting a detector module based on the result of the initial scan to obtain a new system structure, and rapidly calibrating the new system structure; step 3, performing a scan with the new system structure for obtaining activity information of the tested object; step 4, analyzing the activity information of the tested object obtained at step 3. If quality of the activity information can satisfy requirements of the application, the scan is finished; otherwise programming and adjusting the detector module is repeated, rapid calibration is performed, and the activity information of the tested object is obtained again with the new system structure until the activity information satisfies requirements.