Abstract: The present disclosure discloses a method and device for sampling a pulse signal, and a computer program medium.

Abstract: The disclosure discloses methods for determining fitting model for a signal, reconstructing a signal and devices thereof. The determination method may comprise the following steps: segmenting a sampled signal based on collected characteristic information of the signal to obtain a plurality of signal segments; fitting sampling points in the plurality of signal segments using a plurality of fitting models; acquiring fitted values for a parameter of interest in each signal segment based on fitting results; comparing each of the fitted values for the parameter of interest under each of the fitting models with an acquired measurement value for the parameter of interest, and determining a final fitting model for reconstructing the signal among the plurality of the fitting models based on comparison results. In the technical solution provided in the disclosure, the accuracy of the signal reconstruction result and precision of the signal reconstruction may be improved.

Abstract: Provided in the invention is a method and a device of Correction of a ring artifact in a CT image and a computer program medium. The method of correction comprises: pre-processing original detection data; marking a bad detector according to data in the pre-processed original sinogram; acquiring a replacing detection value corresponding to the bad detector by means of a first averaging processing; and performing a CT image reconstruction using a sinogram data after the first averaging processing. The device comprises: a pre-processing unit configured to pre-process original detection data; a marking unit configured to mark a bad detector according to data in the pre-processed original sinogram; a first averaging processing unit configured to acquire a replacing detection value corresponding to the bad detector by means of a first averaging processing; and an image reconstruction unit.

Abstract: A signal sampling method comprising: sampling an electrical signal to be measured using a pre-determined sampling method to obtain a plurality of first sampling points, each of which is represented by a first amplitude and a corresponding first time; measuring a second amplitude of the electrical signal to be measured, wherein the second amplitude is different from the plurality of the first amplitudes; and delaying the electrical signal to be measured, and using the delayed electrical signal to determine a second time when the amplitude of the electrical signal to be measured reaches the second amplitude in order to obtain a second sampling point, which is represented by the second amplitude and the second time. A greater number of sampling points can be sampled, such that the precision of sampling and also the accuracy of subsequent signal restoration may be improved.

Abstract: 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.

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 nuclear detector, comprises a scintillation crystal array including a plurality of scintillation crystal bars of the same size arranged closely and in sequence, a light guide, and a photodetector array including a plurality of photodetectors arranged in sequence. The photodetectors have a cross-sectional area greater than that of the scintillation crystal bars, and the light guide includes a top surface coupled to the scintillation crystal array, an opposed bottom surface coupled to the photodetector array and a side surface. The light guide has a thickness in a range of 0.1 mm to 40 mm. The light guide further includes a slit adjacent to an edge of the light guide, and the slit is configured to extend from the top surface toward the bottom surface of the light guide and the slit has a depth in a range of 0.1 to 0.5 times the thickness of the light guide.

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 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 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: 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 multichannel in-vitro metabolism real-time monitoring apparatus includes a radiation probing apparatus and a constant flow culture apparatus. The constant flow culture apparatus includes a liquid supply bottle, a waste liquid bottle, a multichannel infusion apparatus, and a multichannel liquid separation apparatus. The radiation probing apparatus has two groups of probing modules with flat structures, which are separately disposed on two sides of multichannel biochemical culture apparatuses and are used for recording radiation activities in the multichannel biochemical culture apparatuses in real time.

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 recovering scintillation pulse information. The method comprises the steps: obtaining a scintillation pulse database of unstacked compliance single-events in a low count, and establishing a noise model of a scintillation pulse for the scintillation pulse database of the single-events; calculating a posterior probability logarithm value of a specific energy value according to the noise model of the scintillation pulse; and repeatedly calling the second step by means of calculations, and obtaining an energy value meeting a maximum posterior probability condition. A system for recovering scintillation pulse information. The system comprises a fluctuation model module, a posterior probability module, and an energy value search module.

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: A timing apparatus and method for a radiation detection, measurement, identification, and imaging system are disclosed. The apparatus comprises high-energy photon detectors, a light pulse signal generator and an optical fiber. Each high-energy photon detector comprises a scintillation crystal and an optical-to-electrical conversion multiplying device. The high-energy photon detectors are all provided with light transmission holes. Light pulse signals are propagated to the scintillation crystals through the light transmission holes, then propagated to the surfaces of the optical-to-electrical conversion multiplying devices through the scintillation crystals, converted and multiplied by the optical-to-electrical conversion multiplying devices, and processed and read by an electronic circuit.

Abstract: A channel multiplexing method for reading out a detector signal is provided, including steps: grouping L detectors to form a first source signal and a second source signal; respectively introducing L detector signals into a first signal transmission line including two readout channels A and B and a second signal transmission line including two readout channels C and D, and providing a first signal delay unit and a second signal delay unit on the first signal transmission line and the second signal transmission line; and symbolizing source detectors for forming signals according to pulses of the four readout channels A, B, C and D, and obtaining final pulse information.

Abstract: An on-line energy coincidence method for an all-digital PET system, comprising: a detection module conducting information collection on a scintillation pulse, forming a single event data frame and sending it to an upper computer; the upper computer conducting two-bit position distribution statistics on an incident gamma photon event and conducting position spectrum partition; performing statistics on an energy distribution spectrum of each crystal bar, so as to acquire an energy correction value; the detection module uploading a crystal bar partition data table and an energy peak correction data table; starting information collection of on-line energy correction; when an event is coming, according to a two-dimensional coordinate thereof, from the crystal partition table, searching for a crystal bar number corresponding thereto, and searching for an energy correction value from the energy correction table; and sending data passing the energy coincidence to the upper computer.

Abstract: A method is for acquiring a time point where a glimmering pulse passes over a threshold. The method includes: converting a relationship between a pulse and a threshold into high and low level signals; segmenting output level signals. For a phase where a pulse signal passes over and is higher than a preset threshold and a phase where a pulse signal passes over and is lower than the preset threshold, the two phases respectively include several time points generated by several jumps, and the time point where a pulse passes over a threshold is recorded as any one jump time point or a weighted value of any two or more jump time points. By selecting one jump time point or weighting any two or more jump time points, a more accurate time point where a pulse actually passes over a threshold can be obtained.

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.