WO2020063232A1 - Dispositif de tomographie tep, détecteur de tomographie tep à cristaux multicouches et module de lecture électronique et procédé associé - Google Patents

Dispositif de tomographie tep, détecteur de tomographie tep à cristaux multicouches et module de lecture électronique et procédé associé Download PDF

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Publication number
WO2020063232A1
WO2020063232A1 PCT/CN2019/102536 CN2019102536W WO2020063232A1 WO 2020063232 A1 WO2020063232 A1 WO 2020063232A1 CN 2019102536 W CN2019102536 W CN 2019102536W WO 2020063232 A1 WO2020063232 A1 WO 2020063232A1
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WIPO (PCT)
Prior art keywords
time
energy
layer
signals
pet detector
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English (en)
Chinese (zh)
Inventor
解强强
谢思维
张仁冬
赵指向
杨静梧
黄秋
彭旗宇
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Zhongpai S&t (shenzhen) Co Ltd
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Zhongpai S&t (shenzhen) Co Ltd
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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/29—Measurement performed on radiation beams, e.g. position or section of the beam; Measurement of spatial distribution of radiation
    • G01T1/2914—Measurement of spatial distribution of radiation
    • G01T1/2985—In depth localisation, e.g. using positron emitters; Tomographic imaging (longitudinal and transverse section imaging; apparatus for radiation diagnosis sequentially in different planes, steroscopic radiation diagnosis)
    • Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y02—TECHNOLOGIES OR APPLICATIONS FOR MITIGATION OR ADAPTATION AGAINST CLIMATE CHANGE
    • Y02P—CLIMATE CHANGE MITIGATION TECHNOLOGIES IN THE PRODUCTION OR PROCESSING OF GOODS
    • Y02P70/00—Climate change mitigation technologies in the production process for final industrial or consumer products
    • Y02P70/50—Manufacturing or production processes characterised by the final manufactured product

Definitions

  • the invention relates to the field of positron emission imaging, in particular to a positron emission imaging (PET) device, a multilayer crystal PET detector, an electronic readout module of a multilayer crystal PET detector, and an electronic readout method.
  • PET positron emission imaging
  • Positron Emission and Computed Tomography uses metabolic activity in living organisms as the detection standard, and has a good effect in the early diagnosis of major diseases.
  • PET Positron Emission and Computed Tomography
  • the detector technology composed of discrete crystals as scintillation crystals is the most mature.
  • Discrete crystal detectors use a two-dimensional array of scintillation crystal arrays to couple with photoelectric converters. A discrete discrete crystal is often coupled to a single photoelectric converter.
  • the center of gravity method and light sharing are used to obtain the photon's reaction position and depth (DOI, Depth of Interaction) information.
  • PET detectors composed of discrete crystals have the advantages of simple decoding algorithms, light edge effects, and high spatial resolution. However, because the photons received by traditional discrete crystal detectors reflect in the crystal multiple times before they reach the photoelectric converter, auxiliary methods are needed. In order to obtain the reaction depth information of ⁇ photons.
  • the model of a multilayer crystal PET detector based on discrete crystals is shown in Figure 1.
  • 1 is the detector readout signal cable
  • 2 is the photoelectric converter array
  • 3 is the discrete scintillation crystal array
  • 4 is the multilayer crystal PET detector
  • 5 is the single layer detector
  • the multilayer crystal PET detector can use Kang
  • the depth-of-reaction information can be obtained using the principle of Patterton scattering.
  • the multilayer crystal PET detector shortens the propagation time of ⁇ photons in the crystal and increases the total length of the crystal. Therefore, the time resolution of the detector is improved, and the interception ability of ⁇ photons is improved.
  • the photoelectric converter array in each layer of the multilayer crystal PET detector the total amount of data in the time channel and energy channel of the detector is large, which reduces the processing efficiency of the detector to a certain extent.
  • a multilayer crystal PET detector with high processing efficiency is provided.
  • the multilayer crystal PET detector of the present invention includes an n-layer discrete scintillation crystal array and an n-layer photoelectric converter array.
  • the discrete scintillation crystal array is spaced from the photoelectric converter array.
  • Each layer of the photoelectric converter array includes m photoelectric converters, which are used to convert the optical signals of visible photons detected by them to obtain energy signals and time signals, and the time signals of m photoelectric converters in each layer are combined together, and in each layer The energy signals of the m photoelectric converters are output separately, but the energy signals of the photoelectric converters between the layers are connected in a one-to-one correspondence, so that the multilayer crystal PET detector has m energy channels and n time channels.
  • the energy signals of the photoelectric converters between the layers are connected in series one-to-one correspondingly from the first layer to the n-th layer.
  • n ⁇ m energy signals in the n-layer photoelectric converter array are connected to a hub board through a cable, and the energy signals of the photoelectric converters between the layers on the hub board are connected in a one-to-one correspondence and combined to Obtain m energy channels.
  • an electronic readout module which is used in the above-mentioned multi-layered crystal PET detector and is connected to the photoelectric sensor array.
  • the electronic readout module includes an energy readout circuit and a time reading A circuit for reading energy signals of m energy channels, and a time reading circuit for reading time signals of n time channels.
  • the electronic readout module further includes:
  • n time amplifying circuits one-to-one corresponding to n time channels
  • n time detection circuits one to one corresponding to n comparators
  • the time amplifying circuit is configured to input a time signal to the comparator; the comparator is configured to compare an input time signal with a threshold voltage to obtain an output value and transmit the output value to the time detecting circuit; the time detecting circuit For inputting an output value to the time readout circuit.
  • an electronic readout method of the above-mentioned multilayer crystal PET detector including:
  • Step S100 determine whether there is cross-layer Compton scattering; if not, proceed to step S200; if so, proceed to step S300;
  • Step S200 judging the number of layers of the detector where the reaction is located according to the time signal, and decoding the position and reaction depth information of the gamma photon based on the m energy channel information of the layer;
  • Step S300 Compare the energy levels of different layers based on the time signal, and then determine the layer where the photon reaction is located according to the result of the energy comparison.
  • the output pulse length of the comparator will be different based on the response of different time signals.
  • the pulse width or trigger time of the time signal confirm The location of the response where Compton scattering occurs.
  • a positron emission imaging apparatus which includes a data processing module, the above-mentioned multilayer crystal PET detector, and the above-mentioned electronic readout module, the data processing The module is connected to the electronic readout module and is configured to perform data processing and image reconstruction on the energy signal and the time signal to obtain a scanned image of an object to be imaged.
  • the present invention has the following advantages because the energy channels are merged and the time channels are not merged.
  • the circuit is simpler. It only needs to provide energy channels with the number of single-layer photoelectric converters and time channels with the number of detector layers, and then sufficient data can be collected.
  • reaction depth can be determined according to the time signal of the n layers.
  • the present invention reduces the readout channel, has high processing efficiency, simple circuit implementation, DOI capability, cross-layer Compton calibration capability, and good time performance.
  • FIG. 1 is a model diagram of a multilayer crystal PET detector of the prior art
  • FIG. 2 is an exploded view of a multilayer crystal PET detector according to an embodiment of the present invention.
  • FIG. 3 is a schematic diagram of an electronic readout module used in a multilayer crystal PET detector according to an embodiment of the present invention
  • FIG. 4 is a schematic diagram of comparing the response of different time signals with the output pulse length of the comparator
  • FIG. 5 is a schematic diagram of a positron emission imaging apparatus according to an embodiment of the present invention.
  • the multilayer crystal PET detector 100 includes an n-layer discrete scintillation crystal array 11 and an n-layer photoelectric converter array 12.
  • the 11 and n-layer photoelectric converter arrays 12 are arranged vertically in the height direction, that is, as shown in FIG. 2, in the height direction, a layer of discrete scintillation crystal array, a layer of photoelectric converter array, and a layer of discrete scintillation crystal Array, a layer of photoelectric converter array ...
  • Such an arrangement with a spaced layer is, as shown in FIG. 2, in the height direction, a layer of discrete scintillation crystal array, a layer of photoelectric converter array, and a layer of discrete scintillation crystal Array, a layer of photoelectric converter array ...
  • the multilayer crystal PET detector shown in FIG. 2 includes n-layer detectors, and each single-layer detector includes a layer of discrete scintillation crystal array 11 and a layer of photoelectric converter array 12.
  • each single-layer detector includes a layer of discrete scintillation crystal array 11 and a layer of photoelectric converter array 12.
  • discrete scintillation crystals The array 11 is formed by coupling a plurality of scintillation crystals (the number of rows of the discrete scintillation crystal array 11 is a, the number of columns is b, and the number of the scintillation crystals is a ⁇ b in FIG. 2).
  • the coupled scintillation crystal array has On the upper and lower surfaces, the photoelectric converter array 12 is composed of a plurality of photoelectric sensors (the number of rows of the photoelectric converter array 12 is d, the number of columns is c, and the number of photoelectric sensors is c ⁇ d) in FIG. 2.
  • the photoelectric converter array 12 is coupled to the upper surface of the discrete scintillation crystal array 11.
  • Each photoelectric sensor is coupled to multiple scintillation crystals for detecting visible photons or ultraviolet light generated by the reaction of the gamma photons and the discrete scintillation crystal array 11. , And convert the optical signal of the visible photon it detects to obtain an energy signal and a time signal.
  • the number of layers of the multilayer crystal PET detector is n, where n is greater than 2, the uppermost detector is the top detector, and the lowermost detector is the bottom detector.
  • ⁇ photons can penetrate the first n-1 layer to reach the top detector and be intercepted and converted into ultraviolet or visible light by the scintillation crystal of the top detector. It can also be directly intercepted and converted into ultraviolet or visible light by the scintillation crystal of the bottom detector. Go straight through all discrete scintillation crystal arrays.
  • the energy signals of the photoelectric converters between the layers are connected one-to-one correspondingly in series from the first layer to the n-th layer.
  • Take a 4-layer structure as an example. Assume that each layer has 3 ⁇ 3 9 sensors, output 9 energy signals and 9 time signals. The 9 time signals are directly connected together to form a time signal.
  • the connection method can be as follows:
  • n ⁇ m energy signals in the n-layer photoelectric converter array are connected to a hub board through a cable, and the energy signals of the photoelectric converters between the layers on the hub board are correspondingly connected and combined to obtain m energy channels.
  • the connection method can be as follows: :
  • the present invention provides an electronic readout module 200, which is used in the above-mentioned multilayer crystal PET detector 100 and is connected to the photosensor array 12.
  • the electronic readout module 200 includes an energy readout circuit 21 and Time readout circuit 25, energy readout circuit 21 is connected to m energy channels to read energy signals of m energy channels, time readout circuit 25 and n time channels are used to read time signals of n time channels .
  • the electronic readout module 200 further includes n time amplification circuits 22 1 ..., 22 n , n comparators 23 1 ..., 23 n , and n time detection circuits 24 1 ..., 24 n .
  • the n time amplification circuits 22 1 ??, 22 n are connected to the n time channels T 1 ??, T n in one-to-one correspondence; the n comparators 23 1 ??, 23 n correspond to the n time amplification circuits in one-to-one correspondence Connection; n time detection circuits 24 1 ??, 24 n are connected one-to-one with n comparators.
  • each time amplifying circuit is used to input a time signal to a comparator connected to it; each comparator is used to compare the input time signal with its threshold voltage to obtain an output value and transfer it to a time detection circuit connected to it; A time detection circuit is used to input an output value to the time readout circuit 25.
  • the multilayer crystal PET detector when the multilayer crystal PET detector performs electronic readout, it includes:
  • Step S100 Determine whether there is a cross-layer Compton scattering, if not, go to step S200; if there is, go to step S300, you can judge whether there are cross-layer Compton scattering by the energy of different layers of SiPM, if there is only one layer of SiPM photoelectric
  • the energy signal of the detector indicates that there is no cross-layer Compton scattering phenomenon. If there are energy signals of two or more layers of detectors, it indicates that there is a cross-layer Compton phenomenon;
  • Step S200 judging the number of layers of the detector where the reaction is located according to the time signal, and decoding the position and reaction depth information of the gamma photon based on the m energy channel information of the layer;
  • Step S300 Compare the energy levels of different layers based on the time signal, and then determine the layer where the photon reaction is located according to the result of the energy comparison.
  • the output pulse length of the comparator will be different based on the response of different time signals.
  • the pulse width or trigger time of the time signal confirm The location of the response where Compton scattering occurs.
  • the multilayer crystal PET detector of the present invention performs electronic readout
  • the multilayer detector array receives gamma photons without cross-layer Compton scattering
  • the converter sequence can receive the time signal, so the number of layers of the detector where the reaction is located can be judged according to the time signal.
  • Using the m energy channel information of this layer combined with the positioning algorithm can decode the position and reaction depth information of the gamma photon.
  • the energy depth cannot be directly used to determine the reaction depth, but the n time channels of the photoelectric converters of the n-layer detector are not merged.
  • a positron emission imaging apparatus includes a data processing module 300, the above-mentioned multilayer crystal PET detector 100, and the above-mentioned electronic readout module 200.
  • the data processing module 300 is connected to the electronic readout module 200 and is configured to perform data processing and image reconstruction on the energy information and the time information to obtain a scanned image of the object to be imaged.
  • the data processing module 300 may use a field programmable gate array (FPGA), a digital signal processor (DSP), a complex programmable logic device (CPLD), a micro control unit (MCU), or a central processing unit (CPU).
  • FPGA field programmable gate array
  • DSP digital signal processor
  • CPLD complex programmable logic device
  • MCU micro control unit
  • CPU central processing unit

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  • Physics & Mathematics (AREA)
  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • General Physics & Mathematics (AREA)
  • High Energy & Nuclear Physics (AREA)
  • Molecular Biology (AREA)
  • Spectroscopy & Molecular Physics (AREA)
  • Nuclear Medicine (AREA)
  • Measurement Of Radiation (AREA)

Abstract

La présente invention porte sur un dispositif de tomographie TEP, sur un détecteur de tomographie TEP à cristaux multicouches, ainsi que sur un module de lecture électronique et sur un procédé de lecture électronique pour le détecteur de tomographie TEP à cristaux multicouches (100). Le détecteur de tomographie TEP à cristaux multicouches (100) comprend n couches de réseaux de cristaux de scintillation discrets (11) et n couches de réseaux de convertisseurs photoélectriques (12) ; les réseaux de cristaux de scintillation discrets (11) et les réseaux de convertisseurs photoélectriques (12) sont agencés à des intervalles, chaque couche de réseau de convertisseurs photoélectriques (12) comprend m convertisseurs photoélectriques, chacun des convertisseurs photoélectriques convertit un signal optique pour obtenir un signal d'énergie et un signal de temps ; les signaux de temps des m convertisseurs photoélectriques au niveau de chaque couche sont combinés ensemble, les signaux d'énergie des m convertisseurs photoélectriques au niveau de chaque couche sont émis séparément, mais les signaux d'énergie des convertisseurs photoélectriques entre des couches sont reliés et combinés dans une correspondance biunivoque de telle sorte que le détecteur de tomographie TEP à cristaux multicouches comporte m canaux d'énergie et n canaux de temps.
PCT/CN2019/102536 2018-09-30 2019-08-26 Dispositif de tomographie tep, détecteur de tomographie tep à cristaux multicouches et module de lecture électronique et procédé associé Ceased WO2020063232A1 (fr)

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CN113759415A (zh) * 2020-06-01 2021-12-07 天津市通透医疗科技有限公司 一种获取连续doi信息的新型pet探测器模块

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