51 results about "Pet detector" patented technology

The invention discloses a PET system scanning method, device and equipment and a PET system.The system comprises a PET detector ring with the variable aperture, and the method comprises the steps that the target aperture of the detector ring is determined according to a target scanning part; determining a target calibration file and a target reconstruction strategy according to the target aperture of the detector ring, and controlling the aperture of the detector ring to be adjusted to the target aperture; scanning the target scanning part based on the detector ring of the target aperture and the target calibration file and carrying out data acquisition; and reconstructing an image according to the target calibration file, the target reconstruction strategy and the PET original data. According to the scheme disclosed by the invention, the aperture of the detector ring is adjusted to be the target aperture matched with the target scanning part, scanning and data acquisition are carried out based on the target aperture and the calibration file matched with the target aperture, and imaging is reconstructed based on the calibration file matched with the target aperture and the reconstruction strategy. Therefore, the PET system can be better suitable for scanning of different parts, and the image quality is improved.

The invention discloses a PET detector signal simulation generation method based on artificial intelligence, and the method comprises the steps: generating an initial two-photon signal pair which meets the physical constraints of initial energy and time difference through a two-photon signal generator which fuses Transform and U-Net; decoupling the mixed noise into a plurality of independent physical noise components according to a PET noise physical priori library by using a multi-branch decoupling network based on an attention mechanism, and outputting a pure signal and a noise component map; performing linkage adjustment on the pure signal and the noise component according to a target parameter set by a user through a space-time-noise cooperative regulator; and finally, a customized signal data format is adaptively output according to the downstream task type. According to the method, high-fidelity, interpretable and adjustable coincidence event-level signal simulation is realized, the core problems of complex modeling, noise distortion, lack of relevance and poor scene adaptability of a traditional method are effectively solved, and the efficiency and precision of PET detector research, development and test are remarkably improved.

Disclosed herein are methods and apparatus for acquiring positron emission (or PET) data in the presence of ionizing radiation causing PET detector afterglow. In one variation, the method includes adjusting a coincidence trigger threshold of a PET detector during a treatment session. In one variation, the method includes adjusting a gain factor used in positron emission data acquisition (e.g., a gain factor used to multiply and / or shift an output(s) of a PET detector(s)) during a treatment session. In some variations, a method for acquiring positron emission data during a radiation treatment session includes suspending communication between a PET detector and a signal processor of a controller for a predetermined period of time after a radiation pulse is emitted by a linear accelerator.

The invention discloses a PET detector and a front-end circuit thereof, a scanner and PET-MR equipment, the PET detector comprises a plurality of groups of SiPM arrays, cathodes of the plurality of groups of SiPM arrays are connected, the front-end circuit comprises a first arithmetic unit, the first arithmetic unit is suitable for being connected with the cathodes of each group of SiPM arrays, and the first arithmetic unit is suitable for being connected with the cathodes of the plurality of groups of SiPM arrays; the trigger module is configured to determine trigger time information and energy information according to a total current signal of the multiple groups of SiPM arrays; the second arithmetic unit is configured to determine y-axis coordinate information according to the first anode current of the first target SiPM array and the second anode current of the second target SiPM array; the third arithmetic unit is configured to determine x-axis coordinate information according to the third anode current of the third target SiPM array and the fourth anode current of the fourth target SiPM array; and the data processing unit is configured to determine a crystal position code according to the energy information, the y-axis coordinate information and the x-axis coordinate information. The size of the front-end circuit is small, so that the structural size of the PET detector is reduced, and the effective aperture of the MR scanner is kept.

This application provides a PET detector and a method for analyzing the yellowing of optical adhesives. It relates to the field of optical technology. A light emitting module outputs light sources of at least two wavelengths, including a reference light source. A light receiving module includes light receiving devices configured for each light source, used to receive the light signals from the corresponding light sources and convert the light signals into a first electrical signal. A processing module controls the alternating illumination of different light sources in the light emitting module and collects the first electrical signal output by the light receiving module to determine the first optical parameters of the optical adhesive under the illumination of each light source. Based on the first and second optical parameters, the yellowing value of the optical adhesive is determined. The second optical parameter is determined when the optical adhesive is not in use, based on the first electrical signal collected from the optical adhesive under the illumination of each light source. This allows for real-time and reliable analysis of the yellowing degree of the optical adhesive, ensuring the reliability of the equipment operation.

The invention provides a DNN-based multiplexing PET detector event positioning method and system and a medium, and the method comprises the following steps: simulating and obtaining the spatial characteristics and statistical characteristics of inter-crystal scattering events in a PET detector, and dividing CP events into adjacent CP events and long-distance CP events; generating a training data set in combination with an optical simulation and analysis method, wherein the training data set comprises optical distribution data of CP events and optical distribution data of P events; constructing a multiplexing DNN model, training the multiplexing DNN model by using the data set, inputting optical distribution data to be processed into the trained multiplexing DNN model, and completing event classification; according to different event types, a first interaction crystal is selected, and high-precision event positioning is realized through crystal scattering identification.

The application provides a time correction method and system for inter-crystal scattering events of a PET detector based on SiPM, and the application instantiates multiple time-to-digital converters in a field programmable logic gate array device, performs pulse width measurement on the electrical signals output by each SiPM detector, since the pulse width is positively correlated with the energy of the signal, the non-inter-crystal scattering events and the inter-crystal scattering events can be determined by the pulse width, and the position of the inter-crystal scattering events is determined to reduce the position selection error. During the correction, firstly, the non-inter-crystal scattering events are generally corrected, then further, the time difference between the inter-crystal scattering events occurring in each crystal and the non-inter-crystal scattering events on the response line is counted offline, the additional time difference of each inter-crystal scattering event caused by the time walk effect is obtained, and then the inter-crystal scattering events are secondarily corrected in time online, so that the time resolution of the system is improved.

The application provides a PET detector. The PET detector comprises: a crystal array comprising a plurality of crystal units arranged in a single layer, the crystal units extending in a top-bottom direction and having a top surface, a bottom surface and a side surface between the top surface and the bottom surface; a light reflection film arranged on a surface of at least one crystal unit in the plurality of crystal units; and a semiconductor sensor array comprising a plurality of semiconductor sensors, only part of the crystal units in the crystal array being coupled with the semiconductor sensors, the number of the crystal units in the crystal array being greater than the number of the semiconductor sensors in the semiconductor sensor array. By arranging a light splitting structure on the crystal units, the transmission distance of photons can be effectively shortened relative to arranging a light guide sheet between the crystal array and the semiconductor sensors, and thus the light transmission loss caused by the light guide sheet can be avoided, so that the resolution of the PET detector can be improved.

The application relates to the field of positron emission tomography technology, in particular to a multi-channel high-precision PET circuit acquisition system and a use method thereof, and the system comprises the following: an FPGA control board, which is used for controlling bias voltage programming output voltage values, controlling current programming output voltage values and current values according to DAC bias voltage values received from an upper computer, and sending DUT board configuration information received from the upper computer to a DUT board; and the DUT board, which comprises multi-channel high-precision PET circuits, each circuit is configured through an SPI protocol according to DUT board configuration information received from the upper computer, 16 channels are adopted to collect time electric signal information output by a PET detector, and 64 channels are adopted to collect energy electric signal information output by the PET detector. In the application, the multi-channel high-precision PET circuit acquisition software and the hardware of the control system are portable, the upper computer software program is programmable, and the operation is simple.

The invention provides a PET detector and an optical glue yellowing analysis method. Relates to the technical field of optics. A light emitting module outputs light sources with at least two wavelengths, and the light sources with the at least two wavelengths comprise reference light sources; the light receiving module comprises light receiving devices configured corresponding to the light sources and is used for receiving light signals of the corresponding light sources and converting the light signals into first electric signals; the processing module is used for controlling the different light sources in the light emitting module to be alternately lightened, collecting the first electric signal output by the light receiving module and determining a first optical parameter corresponding to the optical glue under the irradiation of each light source; determining a yellowing value of the optical glue based on the first optical parameter and the second optical parameter; the second optical parameter is an optical parameter determined according to a first electric signal acquired when the optical glue is irradiated by each light source under the condition that the optical glue is not put into use. Therefore, the yellowing degree of the optical glue can be reliably analyzed in real time, and the reliability of equipment operation is ensured.

The present application discloses a PET detector monitoring method, apparatus, storage medium, and electronic device, wherein the method includes: setting an energy collection range of a target energy window based on target radiation emitted by a target component in a target detector, or target radiation emitted by a natural radioactive background; determining target response data based on the target radiation; based on the energy collection range of the target energy window, using each detector unit in a target PET detector to collect energy from the target radiation in real time, obtaining response data corresponding to each detector unit; and monitoring each detector unit based on the target response data and the response data of each detector unit to obtain monitoring results. The monitoring method of the present application does not require an additional radiation source, making monitoring of the PET detector more convenient and faster.

The application relates to a PET detector readout depth acquisition method, a PET image acquisition method, a computer device, a storage medium and a computer program product, which can improve the calibration operability of a detector crystal. The method comprises the following steps: scanning a scanning object in a field of view to obtain scanning data corresponding to the scanning object and received by a coincidence detector crystal; at least one of the coincidence detector crystals is divided into multiple layers, and each layer corresponds to a DOI readout depth; for each layer of the coincidence detector, image reconstruction is performed according to the scanning data received by the layer to determine a reconstruction effect; the reconstruction effect is related to the starting depth of the coincidence response line of the layer; based on the reconstruction effects of the scanning object, the starting depth of the coincidence response line is adjusted until the reconstruction effects of the scanning object in the reconstruction images match; and the DOI readout depth of each layer is obtained according to the current starting depth of the coincidence response line of each layer of the coincidence detector crystal.

The invention provides a detection method and device of a dual-channel PET detector and medical imaging equipment. The detection method of the dual-channel PET detector comprises the following steps: acquiring first detection energy and first detection depth of incident light; according to the first detection energy, the current temperature and a first fitting relation, the actual energy of the incident light is determined, and the first fitting relation represents the mapping relation between the energy gain and the temperature; according to the first detection depth, the current temperature and a second fitting relation, the actual depth of the incident light is determined, and the second fitting relation represents the mapping relation between the detection depth and the temperature. Through the detection method, the correction workload can be reduced, and the detection accuracy of the PET detector can be improved.

The disclosure relates to a device and positron emission tomography (PET) scanner for acquiring a PET image and a system for generating the PET image. The disclosure describes a device that may have one or more moveable portions. The device may comprise an upper portion and a lower portion. The upper portion and lower portion define a cavity for a patient. At least one of the upper portion or the lower portion may be movable. The upper and lower portions may comprise a cap and wings, respectively, At least one of the caps and / or wings may comprise one or more detection modules. The wings may also move with respect to a corresponding cap.

This invention discloses a polyhedral brain PET detector with adjustment function, belonging to the field of medical testing equipment technology. It includes an external support structure, a detection structure, semi-annular pads, and an adjustment module. The detection structure is installed within the external support structure. The detection structure includes a top mounting plate, detection module one, detection module two, detection module three, and a structural assembly frame. Multiple sets of detection modules one, two, and three are installed between the top mounting plate and the structural assembly frame. The top mounting plate, structural assembly frame, detection modules one, two, and three are distributed in a large rhomboid semi-cube shape. Two semi-annular pads are symmetrically installed on the lower side of the external support structure, forming a neck limiter between them. An adjustment structure is installed on the upper side of the external support structure. Through this method, while allowing for a certain degree of deformation adjustment and improving the user's head geometric fit, the peripheral field of vision is effectively reduced.

The invention provides a temperature self-regulation PET detector device which comprises a submodule assembly, the submodule assembly comprises a base, a support and a submodule carrier plate fixed to the base through the support, and the submodule carrier plate is connected with a bimetallic strip structure; the cold plate assembly is in contact with the sub-module carrier plate through the bimetallic strip structure, when the temperature of the sub-module carrier plate rises, the contact area of the bimetallic strip structure and the cold plate assembly is increased, and when the temperature of the sub-module carrier plate drops, the contact area of the bimetallic strip structure and the cold plate assembly is reduced. According to the invention, the temperature between the PET detectors and the temperature between the sub-modules in the detectors can be stabilized in a certain temperature range, and the temperature difference is reduced, so that the image quality of the PET detectors is improved.

This invention relates to the field of positron emission tomography (PET) imaging technology, specifically to a PET detector imaging system and its application. The system includes a shield, a scintillation crystal LYSO array, a silicon photomultiplier tube (SiPM) array, a PET circuit array, an FPGA main control board, a level conversion module, a CameraLink protocol conversion module, and a PC host computer. This invention constructs a model of a large-scale PET detector imaging system, using a high-precision multi-channel PET circuit as the core component. The PET detector (shield + scintillation crystal LYSO array + silicon photomultiplier tube (SiPM) array) is modular. Pulse time window coincidence detection technology is used to encode the accurate location of annihilation, and the acquired energy information is converted and transmitted using the CameraLink protocol. This imaging system is scalable, fully domestically produced, and highly sensitive, and can be effectively applied to ring-type PET detectors in the nuclear medicine field, providing another implementation method and path for large-scale medical diagnostic imaging technology.

An imaging apparatus for imaging ex-vivo tissue specimens includes a positron emission tomography imaging module having at least one pair of PET detectors; a computed tomography imaging module including an X-ray source and an X-ray detector; a tissue specimen receiving element configured to receive the tissue specimen to be imaged.

The application discloses a PET detector signal simulation generation method based on artificial intelligence, comprising the following steps: generating an initial two-photon signal pair meeting initial energy and time difference physical constraints through a two-photon signal generator fusing a Transformer and a U-Net; decoupling mixed noise into multiple independent physical noise components according to a PET noise physical prior library by using a multi-branch decoupling network based on an attention mechanism, and outputting a pure signal and a noise component spectrum; performing linkage adjustment on the pure signal and the noise component according to target parameters set by a user through a space-time-noise collaborative regulator; and finally, outputting a customized signal data format according to a downstream task type. The application realizes high-fidelity, interpretable and controllable coincidence event level signal simulation, effectively solves the core problems of complex modeling, noise distortion, lack of correlation and poor scene adaptability of traditional methods, and significantly improves the efficiency and accuracy of PET detector research and testing.

Provided is a particle detection device and method of fabrication thereof. The particle detection device includes a scintillator array that includes a plurality of scintillator crystals; a plurality of detectors provided on a bottom end of the scintillator array; and a plurality of prismatoids provided on a top end of the scintillator array. Prismatoids of the plurality of prismatoids are configured to redirect particles between top ends of crystals of the scintillator array. Bottom ends of a first group of crystals of the scintillator array are configured to direct particles to a first detector of the plurality of detectors and bottom ends of a second group of crystals of the scintillator array are configured to direct particles to a second detector substantially adjacent to the first detector.

The invention provides a high-resolution depth coding PET detector device, and the device comprises a SiPM pixel module which comprises a SiPM pixel array; the scintillation crystal module comprises a scintillation crystal array, and the SiPM pixel array is optically coupled with the scintillation crystal array; the prismoid light guide module comprises a prismoid light guide array, the prismoid light guide array is optically coupled with the scintillation crystal array, the spatial resolution and DOI resolution of the PET detector module are remarkably improved, meanwhile, good energy resolution and timing resolution are kept, and commercialized popularization is facilitated.

The application discloses a PET detector testing method and device, electronic equipment and a storage medium. The method comprises the following steps: collecting a first dark current signal of a photomultiplier tube cluster of a PET detector, and determining a first state of the photomultiplier tube cluster according to the first dark current signal; or collecting a second dark current signal of a silicon photomultiplier of the PET detector, and determining a second state of the silicon photomultiplier according to the second dark current signal; collecting at least one group of coincidence signals of a detector ring of the PET detector, and determining a third state of a coincidence signal link according to the coincidence signals; and determining a test result of the PET detector by combining any one of the first state and the second state and the third state. The application realizes daily quality inspection testing of the PET detector by computer means without a radioactive source, that is, without a rod source system, and has high testing precision and is convenient to use.

The invention relates to the technical field of nuclear radiation detectors and positron emission tomography (PET) imaging, and discloses a PET detector, a depth positioning method based on the PET detector and a storage medium. The PET detector is composed of a photoelectric detection element array, a crystal array composed of N * M scintillation crystals, a reflecting material and a transparent optical material. The crystal array includes a first end and a second end, and at least one of N and M is greater than 1, at least one of N and M is an odd number, and the first end is coupled to the array of photodetection elements. A reflective material and a transparent optical material are added in gaps between the plurality of scintillation crystals of the crystal array so as to divide the first end into a plurality of first regions to form a first shared optical path and divide the second end into a plurality of second regions to form a second shared optical path. A target first region of the plurality of first regions and a target second region of the plurality of second regions each include a central crystal in the crystal array. And the multiplexing of the scintillation photons is realized through the shared light path.

The application relates to a PET detector dead time correction method, a system and a PET system. The method comprises the following steps: adding a preset trigger signal to an input signal of a PET detector; determining a delay coincidence event of the trigger signal in an output signal of the PET detector; determining a dead time correction factor of the PET detector according to the number of events of the delay coincidence event; and performing dead time correction on the PET detector according to the dead time correction factor. The method can reduce the dead time correction error of the PET detector.

The invention discloses an imaging aperture adjustable PET scanning system and method, and belongs to the technical field of molecular image scanning, the imaging aperture adjustable PET scanning system comprises a PET detector group, a power transmission assembly, an animal bed assembly and a support guide assembly; the power transmission assembly comprises a synchronous pulley, a synchronous belt, a rotating plate and a connecting rod; the supporting and guiding assembly comprises a base and a linear guide rail. The animal bed assembly comprises a sliding table, a lifting table and an animal bed; the PET detector set is assembled on the linear guide rail in a sliding mode, the rotating plate is fixedly connected with the synchronous belt wheels, the synchronous belt wheels are assembled on the shaft ring in a rotating mode, the shaft ring is fixedly connected with the base, the other synchronous belt wheel is in linkage with the output end of the motor, the synchronous belt is wound between the two synchronous belt wheels, and the two ends of the connecting rod are hinged to the rotating plate and the PET detector set respectively. And the connecting rod converts the rotary motion into the translational motion of the PET detector group. According to the invention, by adjusting the imaging aperture of the PET equipment, PET images of experimental animals with different volumes can be obtained.

A scalable medical imaging detector apparatus is provided having interchangeable sensor tiles with fixed external dimensions and fixed or universal mechanical, electrical, and cooling interfaces. Different sensor tile types with different performance levels and production costs are configured with a universal interface for coupling to a medical imaging device, while the rest of the imaging system remains unchanged.

The application discloses a double-end readout PET detector based on continuous crystal light sharing, which comprises N pieces of continuous scintillation crystals, photoelectric converters and signal processing units, and N is greater than or equal to 2; the continuous scintillation crystals are used for blocking gamma rays, converting the gamma rays into scintillation photons and transmitting the scintillation photons to the photoelectric converters; the N pieces of continuous scintillation crystals are arranged into several columns to form an integral structure, and the side surfaces of adjacent continuous scintillation crystals are connected by optical glue; the two end surfaces of each continuous scintillation crystal are connected with a photoelectric converter through optical silicon grease respectively, and are used for generating electrons according to the received scintillation photons and transmitting the electrons to the signal processing units for processing. The application solves the edge effect, thereby being favorable to improving the proportion of the high-resolution area of the detector, improving the positioning precision, having a positive influence on the application of the detector and greatly improving the performance of the PET system.

A Positron Emission Tomography (PET) apparatus according to an embodiment includes processing circuitry. The processing circuitry is configured to determine a virtual detector region on the basis of a Positron Emission Tomography (PET) detector capable of detecting, in a real number coordinate system, a light emission position of an event occurring due to pair annihilation gamma rays becoming incident, a Line Of Response (LOR) defined based on the event detected by the PET detector, and the light emission position and is configured to perform a reconstruction process on the basis of the virtual detector region.

The application discloses a time correction method and device for a multiplexed readout PET detector, aiming at a coincidence event of a PET detector, extracting the amplitude of a signal, calculating the hit position and DOI by using a double-end four-corner readout 8-channel output signal; extracting the time information of the 8-channel output signal, using the amplitude for weighting, obtaining the original time of a coincidence event particle reaching two detectors; establishing a three-dimensional index, so that the original time of the two detectors is equal after subtracting the respective corresponding delay time; establishing an overdetermined equation group about the corresponding delay time of the two detectors, obtaining the delay time corresponding to each three-dimensional index of the two detectors; establishing a three-dimensional index-delay time lookup table, and subtracting the delay time from the original time of each event to obtain the corrected time. The method and device correct the detector signal delay by processing the different channel digital waveforms after multiplexing in the coincidence event, and improve the time precision and imaging quality of the PET.

This application relates to a PET detector and a PET device. The PET detector includes a photoelectric conversion array, which comprises multiple photoelectric converters arranged in an array. A readout circuit assembly includes an insulating substrate, a thin-film electrode disposed on one side of the insulating substrate, and a copper plating layer disposed on the other side of the insulating substrate. The readout circuit assembly is disposed on the photoelectric conversion array, and the thin-film electrode is in electrical contact with the photoelectric conversion array. Current output terminals are provided at each of the four corners of the thin-film electrode, and signal output terminals are provided on the copper plating layer. When current from the photoelectric conversion array flows into the thin-film electrode, time information is obtained through the signal output terminals of the copper plating layer. The PET detector of this application can accurately obtain the position and time information of the PET signal.