WO2018040623A1 - 多伽马光子同时发射药物时间符合核医学成像系统及方法 - Google Patents

多伽马光子同时发射药物时间符合核医学成像系统及方法 Download PDF

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WO2018040623A1
WO2018040623A1 PCT/CN2017/085404 CN2017085404W WO2018040623A1 WO 2018040623 A1 WO2018040623 A1 WO 2018040623A1 CN 2017085404 W CN2017085404 W CN 2017085404W WO 2018040623 A1 WO2018040623 A1 WO 2018040623A1
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gamma photon
gamma
detector
time
imaging system
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PCT/CN2017/085404
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French (fr)
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刘亚强
马天予
范鹏
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清华大学
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Priority to JP2018545651A priority patent/JP6816158B2/ja
Priority to EP17844930.2A priority patent/EP3508885A4/en
Publication of WO2018040623A1 publication Critical patent/WO2018040623A1/zh

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/02—Devices for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/03—Computerised tomographs
    • A61B6/037—Emission tomography
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
    • A61B6/5258—Devices using data or image processing specially adapted for radiation diagnosis involving detection or reduction of artifacts or noise
    • A61B6/5282—Devices using data or image processing specially adapted for radiation diagnosis involving detection or reduction of artifacts or noise due to scatter
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/06—Diaphragms
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/42—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4266—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a plurality of detector units
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
    • A61B6/5205—Devices using data or image processing specially adapted for radiation diagnosis involving processing of raw data to produce diagnostic data
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/54—Control of apparatus or devices for radiation diagnosis
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/16—Measuring radiation intensity
    • G01T1/161—Applications in the field of nuclear medicine, e.g. in vivo counting
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/16—Measuring radiation intensity
    • G01T1/17—Circuit arrangements not adapted to a particular type of detector
    • 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
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/02—Devices for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/03—Computerised tomographs

Definitions

  • the invention belongs to the field of nuclear medicine imaging, and particularly relates to a multi-gamma photon simultaneous drug emission time conforming to a nuclear medicine imaging system and method.
  • Nuclear medicine imaging technology is one of the important technical means for modern medical diagnosis of diseases. It uses radionuclide-labeled molecules to participate in the physiological metabolic process of the organism, and detects X-rays or gamma-photons emitted by radionuclides in vitro and reconstructs the radionuclide by image reconstruction, thereby making it non-invasive. Means to observe the organ metabolism of the organism and obtain diagnostic information of the disease.
  • PET Positron Emission Tomography
  • SPECT Single-Photon Emission Computed Tomography
  • the core components of PET consist of a number of gamma photon detector modules with time measurement and corresponding time-compliance modules.
  • the basic principle of PET involves electron collimation technology, and the radionuclide utilized is a positron nuclides.
  • the positron emitted by the positron nuclides will have a positive and negative electron quenching effect in the living body, producing a pair of gamma photons with an energy of 511 keV and almost opposite directions.
  • Time-adjusted measurement means that if two gamma photon detector modules detect gamma photons of 511 keV in a short period of time (usually in a few nanoseconds), a positive The line of response where the position of electron quenching occurs (approximating the position at which the positron nuclides decay). A large number of such response lines are recorded to obtain a distribution of positron annihilation occurrence positions by image reconstruction, that is, approximately a distribution of positron nuclides in a living body.
  • the core components of SPECT include collimators and gamma photon detector modules.
  • SPECT utilizes a physical collimation technique that utilizes a gamma photon nuclide.
  • a collimator is usually placed at the front end of the gamma photon detector module to limit the angle of incidence of gamma photons emitted by the gamma photon nuclide to the detector so that only gamma photons emitted in a particular direction can pass through the collimator. It was detected by the detector.
  • the gamma photon detector can determine the projection line of the initial emission position of a gamma photon every time a gamma photon is detected, and accumulate a large number of such projection lines to determine the distribution of the initial emission position of the gamma photon by image reconstruction.
  • the SPECT uses a collimator, the emission angle of the gamma photons detectable by the detector is limited, and the detection efficiency of the imaging system is low, which further deteriorates the signal-to-noise ratio of the reconstructed image.
  • Embodiments of the present invention provide a multi-gamma photon simultaneous drug delivery time conforming to a nuclear medicine imaging system, method, device, and computer storage medium, aiming at improving the detection efficiency of the imaging system and the signal to noise ratio of the reconstructed image.
  • Embodiments of the present invention are implemented in such a manner that a multi-gamma photon simultaneously emits a drug time in accordance with a nuclear medicine imaging system, including a plurality of detector probes, a time compliance module, and a computer platform, each of which is configured by a collimator And a gamma photon detector with time measurement function; wherein each collimator is placed at the front end of the corresponding gamma photon detector, so that the gamma photon generated by the decay of the radionuclide in the imaging object is only in the set direction
  • the emission can be detected by the gamma photon detector; the time signal lines of each gamma photon detector are connected with the time matching module, and the time is consistent with the time window set by the module for judging that it is detected by multiple gamma photon detectors respectively.
  • the energy and position signal lines of each gamma photon detector are also connected to the computer platform for multi-gamma The photon meets the validity judgment of the event and the calculation of the projection line where the gamma photon emission position is located to obtain the radiation Nuclides decay position.
  • Another object of the present invention is to provide an imaging method for the above imaging system, the method comprising the steps of: (1) starting the imaging system, setting an acquisition time of the imaging system, and setting a time according to a module time. Window width; setting a plurality of energy windows of the gamma photon detector according to the gamma photon energy emitted by the radionuclide used; setting a length threshold for multi-gamma photon compliance event validity determination; injecting radioactivity into the imaging object (2)
  • the computer platform determines whether the imaging process ends according to the set acquisition time; if it is finished, step (5) is performed; if not, step (3) is performed; (3) the time conforms to the module judgment gamma Whether the photon detector detects a multi-gamma photon compliance event, if it is detected, step (4) is performed; if not, step (2) is performed; (4) the computer platform inputs according to the gamma photon detector
  • the plurality of gamma photon event energy information determines whether the plurality
  • Another object of embodiments of the present invention is to provide an apparatus comprising: one or more processors; a memory; one or more programs, the one or more programs being stored in the memory when Or when the plurality of processors are executed, the imaging method described in the above embodiment is performed.
  • Another object of embodiments of the present invention is to provide a non-volatile computer storage medium storing one or more programs, when the one or more programs are executed by a device, The apparatus performs the imaging method described in the above embodiments of the present invention.
  • the imaging system of the embodiment of the invention effectively overcomes the defect that the conventional PET or SPECT system can only determine the response line or projection line of the radionuclide decay position and cannot determine the specific position of the radionuclide decay occurring on the response line or the projection line. Realizing the localization of the decay position of the radionuclide by calculating the position of the shortest point of the distance between the projection lines determined by the two or more gamma photons emitted by the non-parallel cascade, thereby realizing the radionuclide in the living body Acquisition of distribution.
  • the decay position of the radionuclide can be calculated based on a plurality of non-parallel projection lines, the image reconstruction algorithm is simplified, and the signal-to-noise ratio of the reconstructed image is improved.
  • the demand for the total count of gamma photon events is reduced, the dose of radionuclide ingested by the patient is reduced, and the radiation of the patient is reduced to some extent. According to the risk.
  • FIG. 1 is a schematic view of an imaging system employing a parallel hole collimator in an embodiment of the present invention
  • Figure 2 is a schematic illustration of an imaging system employing a pinhole collimator
  • FIG. 3 is a flow chart of an imaging method of the imaging system of FIG. 1 or 2.
  • the invention provides a multi-gamma photon simultaneous emission medicine time conforming to nuclear medicine imaging system and method, which is described in detail with reference to the accompanying drawings and embodiments as follows:
  • FIG. 1 The overall structure of the imaging system of this embodiment is as shown in FIG. 1 , which is composed of two detector probes, a time matching module 3 and a computer platform 4, which are arranged perpendicularly to each other, and each detector probe is composed of a parallel hole collimator 1 And a gamma photon detector 2 having a time measuring function; wherein each parallel hole collimator 1 is respectively placed at a front end of the gamma photon detector 2 corresponding thereto to cause a multi-gamma generated by decay of radionuclides in the imaging object 5 The photon can only be detected by the gamma photon detector 2 in the direction perpendicular to the gamma photon detector surface.
  • the imaging object 5 can be a living body or a standardized imaging model of the nuclear medicine imaging system; each gamma photon detection
  • the time signal lines of the device 2 are all connected to the time compliance module 3, which sets a time window of a certain width (the time window width is adjustable according to the radionuclide used, usually within a few hundred nanoseconds) for judging respectively Whether multiple gamma photon events detected by two gamma photon detectors constitute a multi-gamma photon compliance event, and input corresponding judgment results to the computer In stage 4; each energy gamma photon detector 2 and the position signal line is also connected to the computer platform 4 for calculating the projection line gamma photon emission so as to acquire the location position of radionuclide decays.
  • the parallel hole collimator 1 used in this embodiment is composed of a rectangular tungsten alloy plate, wherein the tungsten alloy material has a strong absorption effect on gamma photons.
  • a plurality of parallel collimating holes are provided at equal intervals on the rectangular plate so that only gamma photons emitted along the holes can be detected by the gamma photon detector 2 through the collimator.
  • the collimator used in this embodiment has a thickness of 4 mm, the collimation hole has a hole diameter of 2 mm, and the hole wall has a thickness of 2 mm.
  • the gamma photon detector 2 is a NaI (Tl) scintillator detector, and the scintillator is a monolithic continuous NaI (Tl) crystal having a size of 585 mm (length) ⁇ 470 mm (width) ⁇ 9.5. Mm (thickness); 55 photomultipliers (PMT) are coupled to the end of the NaI (Tl) crystal away from the collimator for photoelectric signal conversion to achieve gamma photon position, energy and in the crystal Time measurement.
  • Tl NaI
  • PMT photomultipliers
  • the radionuclide labeled by the drug used in the imaging system of the present invention may be other multi-gamma photon radionuclides in addition to indium 111, that is, the radionuclide can generate at least in a cascade manner in a short time during the decay process.
  • Two gamma photons including but not limited to sodium 22, iodine 131, ⁇ 201, ⁇ 82, ⁇ 90, and the like.
  • the type of collimator used in the imaging system of the present invention may be a pinhole type collimator (as shown in FIG. 2), a convergent type collimator, and a divergent type collimation in addition to the parallel hole collimator shown in FIG. And so on.
  • the collimators are conventional products, and the types and parameters of the collimators used can be selected according to the imaging field size, spatial resolution and detection efficiency of the imaging system to be achieved.
  • the number of detector probes used in the imaging system of the present invention may be two or more.
  • the detection planes of the plurality of detector probes are arranged in a non-parallel manner such as a ring, a square or a polygon.
  • Detector probe The number and arrangement of the imaging system can be selected according to the detection efficiency of the imaging system to be achieved. When the number of detector probes is larger, the detection efficiency of the imaging system is higher.
  • FIG. 3 The imaging method of the imaging system of the present invention is shown in FIG. 3, and the specific implementation steps of the method are described as follows:
  • the imaging system setting the acquisition time to 20 minutes, setting the time window width of the module 3 to 200 ns; setting the length threshold for multi-gamma photon event validity judgment to 5 mm, the length
  • the threshold can be adjusted according to the type and parameters of the collimator used in the imaging system and the spatial resolution of the gamma photon detector 2; the energy of the gamma photon detector 2 can be set according to the gamma photon energy emitted by the gamma photon radionuclide used. window.
  • the gamma photon radionuclide used in this embodiment is indium 111, which can be produced in a cascade manner in a short period of time (depending on the radionuclide used, usually within a few hundred nanoseconds) during the decay process.
  • the gamma photon has energy of 171 keV and 245 keV, respectively, so the energy window of the gamma photon detector 2 is set to 171 keV ⁇ 10% and 245 keV ⁇ 10%, respectively; wherein the energy window of each gamma photon detector 2
  • the number can be adjusted according to the number of gamma photons emitted by the radionuclide cascade used, that is, the gamma photon of each energy corresponds to one energy window; the width of each energy window can be based on the energy of the gamma photon detector 2 Resolution adjustment; a radioactive drug labeled with indium 111 was injected into the imaging subject 5 with an activity of 4 mCi.
  • the computer platform 4 determines whether the imaging process ends according to the set acquisition time; if it is finished, step (5) is performed; if not, step (3) is performed;
  • the time matching module 3 determines whether the gamma photon detector 2 detects a multi-gamma photon compliance event, and if it is detected, performs step (4); if not, performs step (2);
  • the gamma photon coincides with the event that two or more gamma detected if two or more gamma photon events detected by multiple gamma photon detectors coincide with the time window set by module 3
  • the photon event constitutes a multi-gamma photon coincidence event;
  • the computer platform 4 determines, according to the two gamma photon event energy information input by the gamma photon detector 2, whether the input two gamma photon energies are respectively within the set two energy windows; Within the two energy windows set, the multi-gamma photon coincidence event is discarded; if respectively within the two energy windows set, the two gamma photon events input according to the gamma photon detector 2
  • the position information calculates a projection line at which the gamma photon decays; the non-parallel two determined by all gamma photon events are calculated (the number of projection lines is at least 2, and no more than the gamma photon nuclide level used) The number of gamma photons emitted by the joint)
  • the position of the shortest point of the sum of the distances of the projection lines (each gamma photon event in the multi-gamma photon event can determine the projection line where a gamma photon emission position is located) , determining whether
  • the distribution of the radionuclide in the imaged subject is obtained according to the decay position of the radionuclide calculated by all the multi-gamma photon coincidence events.
  • the imaging system in the embodiment of the invention simplifies the image reconstruction algorithm and improves the signal-to-noise ratio of the reconstructed image because the decay position of the radionuclide can be obtained by direct calculation.
  • the spatial distribution of radionuclides reduces the need for a total count of gamma photon events, reduces the dose of radionuclide ingested by patients, and reduces the risk of radiation exposure to a certain extent.
  • the imaging method of the present invention is programmed (this process can be implemented by a programmer through conventional programming techniques) and then input into the computer platform 4, and the desired effect of the imaging method can be achieved according to the step execution.
  • Embodiments of the present invention also disclose an apparatus comprising: one or more processors; a memory; one or more programs, the one or more programs being stored in the memory when the one or more When the processors are executed, the imaging method of the imaging system described in the above embodiments is performed.
  • Embodiments of the present invention also disclose a non-volatile computer storage medium storing one or more programs that, when executed by a device, cause the device to perform the present invention
  • the imaging method of the imaging system of the above embodiment is also disclosed.

Abstract

一种基于多伽马光子同时发射药物的时间符合核医学成像系统及方法，该系统包括：多个以非平行方式排列的探测器探头、时间符合模块（3）以及计算机平台（4）构成，每个探测器探头均由准直器（1）和具备时间测量功能的伽马光子探测器（2）构成，探测放射性核素在很短时间内放射的多个伽马光子构成多伽马光子符合事件；该方法计算到多伽马光子符合事件中的每一个伽马光子事件所确定的投影线的距离之和最短的点的位置即为放射性核素发生衰变的位置，积累一定数量的多伽马光子符合事件即可实现放射性核素在生物体内分布的获取。该成像系统和方法简化了重建算法，提高了重建图像的信噪比，降低了对伽马光子总计数的需求，降低了病人的辐照风险。

Description

多伽马光子同时发射药物时间符合核医学成像系统及方法
相关申请的交叉引用
本申请要求清华大学于2016年8月31日递交的、发明名称为“多伽马光子同时发射药物时间符合核医学成像系统及方法”的，中国专利申请号为“201610798146.4”的优先权。
技术领域
本发明属于核医学影像领域，特别涉及一种多伽马光子同时发射药物时间符合核医学成像系统及方法。
背景技术
核医学影像技术是现代医学进行疾病诊断的重要技术手段之一。它利用放射性核素标记的分子参与生物体的生理代谢过程，在生物体外探测放射性核素发出的X射线或伽马光子并通过图像重建即可得到放射性核素的分布，从而以非侵入式的手段观察生物体的器官代谢情况，获取疾病的诊断信息。在核医学影像领域，最为重要的两种成像系统分别是正电子发射断层成像仪(Positron Emission Tomography,以下简称PET)和单光子发射计算机断层成像仪(Single-Photon Emission Computed Tomography,以下简称SPECT)。目前PET和SPECT均已广泛用于临床检查和诊断，包括癌症、神经系统疾病和心血管疾病等。
PET的核心组件由很多个具备时间测量功能的伽马光子探测器模块以及相应的时间符合模块构成。PET的基本原理涉及电子准直技术，所利用的放射性核素为正电子核素。正电子核素放射出的正电子会在生物体内发生正负电子湮灭效应，产生一对能量为511keV、方向几乎相反的伽马光子。采用时间符合测量手段，即如果两个伽马光子探测器模块在一个很短的时间内(通常在几个纳秒)分别探测到这两个能量为511keV的伽马光子，就能确定一条正电子湮灭的发生位置(近似为正电子核素发生衰变的位置)所在的响应线(Line of Response)。记录大量这样的响应线通过图像重建即可获得正电子湮灭发生位置的分布，即近似为正电子核素在生物体内的分布。由于正电子湮灭产生的一对伽马光子的发射方向是几乎相反的，因此只能确定正电子湮灭的发生位置在相应的响应线上，而不能确定正电子湮灭发生在相应响应线上的具体位置。尽管可以通过飞行时间(Time-of-Flight)测量技术初步确定正电子湮灭发生在相应响应线上的位置范围，但这需要伽马光子探测器模块具备极高的时间分辨率。由于正电子湮灭在响应线上发生位置的不确定性，重建的正电子 核素在生物体内分布图像的信噪比往往较低，影响诊断的效果。为提高图像信噪比通常需要累积大量的响应线，而这会使得病人摄入较大剂量的正电子核素，增加病人的辐照风险。
SPECT的核心组件包括准直器及伽马光子探测器模块等。SPECT利用的是物理准直技术，其所利用的核素为伽马光子核素。在伽马光子探测器模块的前端通常会放置准直器来限制伽马光子核素放射出的伽马光子到达探测器的入射角度，使得仅沿特定方向发射的伽马光子才能通过准直器被探测器探测到。伽马光子探测器每探测到一个伽马光子就能确定一条伽马光子初始发射位置所在的投影线，积累大量这样的投影线通过图像重建就能确定伽马光子初始发射位置的分布，即伽马光子核素在生物体内的分布。与PET存在类似的缺陷，SPECT也不能确定伽马光子在投影线上的具体发射位置，因此重建图像的信噪比较差。另外由于SPECT使用了准直器，限制了能被探测器探测到的伽马光子的发射角度，成像系统的探测效率较低，而这进一步使得重建图像的信噪比恶化。
发明内容
本发明实施例提供一种多伽马光子同时发射药物时间符合核医学成像系统、方法、设备及计算机存储介质，旨在提升成像系统的探测效率和重建图像的信噪比。
本发明实施例是这样实现的，一种多伽马光子同时发射药物时间符合核医学成像系统，包括多个探测器探头、时间符合模块以及计算机平台构成，每个探测器探头均由准直器和具备时间测量功能的伽马光子探测器构成；其中，各个准直器分别放置在与其对应的伽马光子探测器前端使得成像对象内放射性核素发生衰变产生的伽马光子仅沿设定方向发射才能被伽马光子探测器探测到；各伽马光子探测器的时间信号线均与时间符合模块连接，时间符合模块设定的时间窗用于判断分别被多个伽马光子探测器探测到的多个伽马光子事件是否构成多伽马光子符合事件，并将判断结果输入到计算机平台中；各伽马光子探测器的能量和位置信号线还同时与计算机平台连接，用于多伽马光子符合事件的有效性判断以及伽马光子发射位置所在投影线的计算从而获得放射性核素的衰变位置。
本发明实施例的另一目的在于提供一种上述成像系统的成像方法，该方法包括以下步骤：(1)启动所述成像系统，设定该成像系统的采集时间，设定时间符合模块的时间窗宽度；依据所用放射核素所放射的伽马光子能量设定伽马光子探测器的多个能窗；设定用于多伽马光子符合事件有效性判断的长度阈值；向成像对象注射放射性核素；(2)计算机平台根据所设定的采集时间判断成像过程是否结束；若结束，则执行步骤(5)；若未结束，则执行步骤(3)；(3)时间符合模块判断伽马光子探测器是否探测到多伽马光子符合事件，若探测到，则执行步骤(4)；若未探测到，则执行步骤(2)；(4)计算机平台根据伽马光子探测器输入的多个伽马光子事件能量信息判断所输入的多个伽马光子能量是否分别在所 设定的多个能窗内；如果分别不在所设定的多个能窗内，则舍弃该多伽马光子符合事件；如果分别在所设定的多个能窗内，则根据伽马光子探测器所输入的多个伽马光子事件的位置信息计算伽马光子发生衰变所在位置的投影线；计算到所有伽马光子事件所确定的非平行的多条投影线的距离之和最短的点的位置，判断该点到任意一条投影线的距离是否都小于等于所设定的长度阈值，如果小于等于所设定的长度阈值，则记录放射性核素发生衰变的位置为该点位置；如果该线段长度大于所设定的长度阈值，则舍弃该多伽马光子符合事件；执行步骤(2)；所述投影线的条数至少为2，且不多于所用伽马光子核素级联发射的伽马光子的个数；(5)根据所有多伽马光子符合事件计算的放射性核素的衰变位置得到放射性核素在成像对象体内的分布。
本发明实施例的另一目的在于提供一种设备，包括：一个或者多个处理器；存储器；一个或者多个程序，所述一个或者多个程序存储在所述存储器中，当被所述一个或者多个处理器执行时，执行上述实施例所述成像方法。
本发明实施例的另一目的在于提供一种非易失性计算机存储介质，所述计算机存储介质存储有一个或者多个程序，当所述一个或者多个程序被一个设备执行时，使得所述设备执行本发明上述实施例所述的成像方法。
本发明实施例的成像系统，有效地克服了传统PET或SPECT系统只能确定放射性核素衰变位置所在响应线或投影线而不能确定放射性核素衰变发生在响应线或投影线上具体位置的缺陷，通过计算到非平行级联发射的两个及以上伽马光子所确定的投影线的距离之和最短的点的位置实现对放射性核素的衰变位置的定位，从而实现放射性核素在生物体内分布的获取。由于能够基于多条非平行投影线计算放射性核素的衰变位置，简化了图像重建算法，提高了重建图像的信噪比。同时由于不需要累积大量的投影线来重建放射性核素的空间分布，降低了对伽马光子事件总计数的需求，减少了病人摄入的放射性核素剂量，一定程度上降低了病人的放射辐照风险。
附图说明
为了更清楚地说明本发明实施例中的技术方案，下面将对实施例或现有技术描述中所需要使用的附图作简单地介绍，显而易见地，下面描述中的附图仅仅是本发明的一些实施例，对于本领域普通技术人员来讲，在不付出创造性劳动性的前提下，还可以根据这些附图获得其他的附图。
图1是本发明实施例中的采用平行孔准直器的成像系统的示意图；
图2是采用针孔准直器的成像系统的示意图；
图3是图1或图2中的成像系统的成像方法流程图。
具体实施方式
本发明提出的一种多伽马光子同时发射药物时间符合核医学成像系统及方法结合附图以及实施例详细说明如下：
本实施例的成像系统总体结构如图1所示，由探测平面互相垂直排列的两个探测器探头、时间符合模块3以及计算机平台4构成，每个探测器探头均由平行孔准直器1和具备时间测量功能的伽马光子探测器2构成；其中各个平行孔准直器1分别放置在与其对应的伽马光子探测器2前端使得成像对象5内放射性核素发生衰变产生的多伽马光子仅沿垂直于伽马光子探测器面方向发射才能被伽马光子探测器2探测到，成像对象5可以为生物体，也可以为核医学成像系统的标准化成像模型；每个伽马光子探测器2的时间信号线均连接到时间符合模块3，该模块设定一定宽度的时间窗(时间窗宽度根据所采用的放射性核素可调，通常在几百纳秒以内)用于判断分别被两个伽马光子探测器探测到的多个伽马光子事件是否构成多伽马光子符合事件，并将相应的判断结果输入到计算机平台4中；每个伽马光子探测器2的能量和位置信号线也连接到计算机平台4用于伽马光子发射位置所在投影线的计算从而获取放射性核素的衰变位置。
本实施例中所用平行孔准直器1由矩形钨合金板组成，其中钨合金材料对伽马光子具有较强的吸收作用。在该矩形板上等间隔地设置了多个平行的准直孔，使得仅沿该孔发射的伽马光子才能穿过准直器被伽马光子探测器2探测到。本实施例中所用准直器的厚度为4mm,准直孔的孔径为2mm，孔壁的厚度为2mm。
本实施例中伽马光子探测器2为NaI(Tl)闪烁体探测器，所采用闪烁体为一整块连续的NaI(Tl)晶体，其尺寸为585mm(长)×470mm(宽)×9.5mm(厚)；在NaI(Tl)晶体远离准直器的一端耦合着55个光电倍增管(Photomultiplier,以下简称PMT)，用于光电信号转换从而实现伽马光子在晶体内作用位置、能量和时间的测量。
本发明成像系统所用药物所标记的放射性核素除铟111外，还可以是其他多伽马光子放射核素，即该放射性核素在衰变过程中能以级联方式在很短时间内产生至少两个伽马光子，包括但不限于钠22、碘131、铊201、铷82、钇90等。
本发明成像系统所用准直器的种类除图1所展示的平行孔准直器外，还可以是针孔型准直器(如图2所示)、汇聚型准直器、发散型准直器等。所述准直器均为常规产品，可根据所要达到的成像系统成像视野大小、空间分辨率及探测效率等因素选择所用准直器类型和参数。
本发明成像系统所用探测器探头的个数除本实施例中的两个外，还可以是两个以上，多个探测器探头的探测平面以环形、方形或多边形等非平行的方式排列布置。探测器探头 的个数及排列方式可根据所要达到的成像系统的探测效率进行选择，当探测器探头的个数越多时，则成像系统的探测效率越高。
本发明成像系统的成像方法流程如图3所示，结合实施例对该方法的具体实施步骤说明如下：
(1)启动所述成像系统，设定采集时间为20分钟，设定时间符合模块3的时间窗宽度为200ns；设定用于多伽马光子事件有效性判断的长度阈值为5mm，该长度阈值可根据成像系统所用准直器类型和参数以及伽马光子探测器2的空间分辨率调节；依据所用伽马光子放射核素所放射的伽马光子能量设定伽马光子探测器2的能窗。本实施例中所用伽马光子放射核素为铟111，其在衰变过程中能以级联方式在很短的时间内(取决于所用放射性核素，通常在几百纳秒内)产生两个伽马光子，其能量分别为171keV和245keV，因此设定伽马光子探测器2的能窗均分别为171keV±10％和245keV±10％；其中每个伽马光子探测器2的能窗的个数均可根据所用放射性核素级联发射的伽马光子的个数调节，即每种能量的伽马光子对应一个能窗；每个能窗的宽度可根据伽马光子探测器2的能量分辨率调节；向成像对象5注射活度为4mCi由铟111标记的放射性药物。
(2)计算机平台4根据所设定的采集时间判断成像过程是否结束；若结束，则执行步骤(5)；若未结束，则执行步骤(3)；
(3)时间符合模块3判断伽马光子探测器2是否探测到多伽马光子符合事件，若探测到，则执行步骤(4)；若未探测到，则执行步骤(2)；所述多伽马光子符合事件，即如果被多个伽马光子探测器探测到的两个及以上伽马光子事件在时间符合模块3所设定的时间窗内，则所探测的两个及以上伽马光子事件构成多伽马光子符合事件；
(4)计算机平台4根据伽马光子探测器2输入的两个伽马光子事件能量信息判断所输入的两个伽马光子能量是否分别在所设定的两个能窗内；如果分别不在所设定的两个能窗内，则舍弃该多伽马光子符合事件；如果分别在所设定的两个能窗内，则根据伽马光子探测器2所输入的两个伽马光子事件的位置信息计算伽马光子发生衰变所在位置的投影线；计算到所有伽马光子事件所确定的非平行的两条(投影线的条数至少为2，且不多于所用伽马光子核素级联发射的伽马光子的个数)投影线(多伽马光子符合事件中的每一个伽马光子事件均可以确定一条伽马光子发射位置所在的投影线)的距离之和最短的点的位置，判断该点到任意一条投影线的距离是否都小于等于所设定的长度阈值，如果小于等于所设定的长度阈值，则记录放射性核素发生衰变的位置为该点位置；如果该线段长度大于所设定的长度阈值，则舍弃该多伽马光子符合事件；执行步骤(2)；
(5)根据所有多伽马光子符合事件计算的放射性核素的衰变位置得到放射性核素在成像对象体内的分布。
本发明实施例中的成像系统由于能够通过直接计算方式获得放射性核素的衰变位置，简化了图像重建算法，提高了重建图像的信噪比。同时由于不需要累积大量的投影线来重 建放射性核素的空间分布，降低了对伽马光子事件总计数的需求，减少了病人摄入的放射性核素剂量，一定程度上降低了病人的放射辐照风险。
将本发明所述成像方法进行编程(该过程可由编程人员通过常规的编程技术予以实现)后输入到计算机平台4中，按照步骤执行即可实现该成像方法预期达到的效果。
本发明的实施例还公开了一种设备，包括：一个或者多个处理器；存储器；一个或者多个程序，所述一个或者多个程序存储在所述存储器中，当被所述一个或者多个处理器执行时，执行上述实施例所述的成像系统的成像方法。
本发明的实施例还公开了一种非易失性计算机存储介质，计算机存储介质存储有一个或者多个程序，当所述一个或者多个程序被一个设备执行时，使得所述设备执行本发明上述实施例的成像系统的成像方法。
另外，本发明实施例的批量化生产的多层微流体芯片制作方法、系统和非易失性计算机存储介质的其它构成以及作用对于本领域的技术人员而言都是已知的，为了减少冗余，不做赘述。
在本说明书的描述中，参考术语“一个实施例”、“一些实施例”、“示例”、“具体示例”、或“一些示例”等的描述意指结合该实施例或示例描述的具体特征、结构、材料或者特点包含于本发明的至少一个实施例或示例中。在本说明书中，对上述术语的示意性表述不一定指的是相同的实施例或示例。而且，描述的具体特征、结构、材料或者特点可以在任何的一个或多个实施例或示例中以合适的方式结合。
尽管已经示出和描述了本发明的实施例，本领域的普通技术人员可以理解：在不脱离本发明的原理和宗旨的情况下可以对这些实施例进行多种变化、修改、替换和变型，本发明的范围由权利要求及其等同限定。

Claims (6)

  1. 一种多伽马光子同时发射药物时间符合核医学成像系统，其特征在于，包括多个探测器探头、时间符合模块以及计算机平台构成，每个探测器探头均由准直器和具备时间测量功能的伽马光子探测器构成；其中，各个准直器分别放置在与其对应的伽马光子探测器前端使得成像对象内放射性核素发生衰变产生的伽马光子仅沿设定方向发射才能被伽马光子探测器探测到；各伽马光子探测器的时间信号线均与时间符合模块连接，时间符合模块设定的时间窗用于判断分别被多个伽马光子探测器探测到的多个伽马光子事件是否构成多伽马光子符合事件，并将判断结果输入到计算机平台中；各伽马光子探测器的能量和位置信号线还同时与计算机平台连接，用于多伽马光子符合事件的有效性判断以及伽马光子发射位置所在投影线的计算从而获得放射性核素的衰变位置。
  2. 如权利要求1所述的基于多伽马光子同时发射药物的时间符合核医学成像系统，其特征在于，所述多个探测器探头，至少包含两个探测器探头；当采用两个探测器探头时，两个探测器探头的探测平面以互相垂直或其他非平行的方式排列布置；当采用两个以上探测器探头时，多个探测器探头的探测平面以非平行的方式排列布置。
  3. 如权利要求2所述的基于多伽马光子同时发射药物的时间符合核医学成像系统，其特征在于，所述放射性核素，在其衰变过程中能以级联方式在很短时间内产生至少两个伽马光子。
  4. 一种采用如权利要求3所述成像系统的成像方法，其特征在于，该方法包括以下步骤：
    (1)启动所述成像系统，设定该成像系统的采集时间，设定时间符合模块的时间窗宽度；依据所用放射核素所放射的伽马光子能量设定伽马光子探测器的多个能窗；设定用于多伽马光子符合事件有效性判断的长度阈值；向成像对象注射放射性核素；
    (2)计算机平台根据所设定的采集时间判断成像过程是否结束；若结束，则执行步骤(5)；若未结束，则执行步骤(3)；
    (3)时间符合模块判断伽马光子探测器是否探测到多伽马光子符合事件，若探测到，则执行步骤(4)；若未探测到，则执行步骤(2)；
    (4)计算机平台根据伽马光子探测器输入的多个伽马光子事件能量信息判断所输入的多个伽马光子能量是否分别在所设定的多个能窗内；如果分别不在所设定的多个能窗内，则舍弃该多伽马光子符合事件；如果分别在所设定的多个能窗内，则根据伽马光子探测器所输入的多个伽马光子事件的位置信息计算伽马光子发生衰变所在位置的投影线；计算到所有伽马光子事件所确定的非平行的多条投影线的距离之和最短的点的位置，判断该点到 任意一条投影线的距离是否都小于等于所设定的长度阈值，如果小于等于所设定的长度阈值，则记录放射性核素发生衰变的位置为该点位置；如果该线段长度大于所设定的长度阈值，则舍弃该多伽马光子符合事件；执行步骤(2)；所述投影线的条数至少为2，且不多于所用伽马光子核素级联发射的伽马光子的个数；
    (5)根据所有多伽马光子符合事件计算的放射性核素的衰变位置得到放射性核素在成像对象体内的分布。
  5. 一种设备，其特征在于，包括：
    一个或者多个处理器；
    存储器；
    一个或者多个程序，所述一个或者多个程序存储在所述存储器中，当被所述一个或者多个处理器执行时，执行如权利要求4所述的成像方法。
  6. 一种非易失性计算机存储介质，其特征在于，所述计算机存储介质存储有一个或者多个程序，当所述一个或者多个程序被一个设备执行时，使得所述设备执行如权利要求4所述的成像方法。
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