WO2020078013A1 - 探测装置、包括该探测装置的成像系统及其探测方法 - Google Patents

探测装置、包括该探测装置的成像系统及其探测方法 Download PDF

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WO2020078013A1
WO2020078013A1 PCT/CN2019/090910 CN2019090910W WO2020078013A1 WO 2020078013 A1 WO2020078013 A1 WO 2020078013A1 CN 2019090910 W CN2019090910 W CN 2019090910W WO 2020078013 A1 WO2020078013 A1 WO 2020078013A1
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Prior art keywords
detector
detection device
target area
layer
collimator
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PCT/CN2019/090910
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English (en)
French (fr)
Inventor
朱珂璋
谢庆国
代平平
梅峻骅
苏禹鸣
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苏州瑞派宁科技有限公司
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Publication of WO2020078013A1 publication Critical patent/WO2020078013A1/zh

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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
    • G01T1/16—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
    • G01T1/178—Circuit arrangements not adapted to a particular type of detector for measuring specific activity in the presence of other radioactive substances, e.g. natural, in the air or in liquids such as rain water

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  • the present application relates to the field of radiation detection applications, and in particular, to a detection device, an imaging system including the detection device, and a detection method thereof.
  • Nuclear medicine imaging is a modern medical imaging technology that injects a tracer labeled with a radionuclide capable of producing gamma photons or positrons into the human body, and detects the radiation generated by the radionuclide outside the human body. Tracer distribution and change information in the human body, which can be used for the diagnosis and treatment of diseases. Nuclear medical imaging is a typical molecular imaging method, which can reflect the physiological, metabolic, functional, and molecular information in the human body, and is one of the current mainstream medical imaging methods.
  • Nuclear medicine imaging technology mainly includes positron emission tomography (Positron Emission Tomography, referred to as PET) and single photon emission computerized tomography (Single Photon Emission Computerized Tomography, referred to as SPECT) these two technologies.
  • PET technology and SPECT technology are mainly to detect the distribution and change information of drugs marked with radionuclides emitting positrons and single photons in the human body.
  • a radionuclide-labeled drug is usually injected into the human body, and then the detector inside the device is used to surround the human body from different angles Collecting the optical signal generated by the medicine in the human body, converting the collected optical signal into an electrical signal and reconstructing the electrical signal, so that the lesion part and the lesion type in the human body can be determined according to the obtained reconstructed image.
  • the SPECT imaging device can be used to perform 99mTc-diethylacetanilide iminodiacetic acid (EHIDA) dynamic imaging of the liver and gallbladder, so that it can be detected whether the baby has congenital biliary atresia.
  • EHIDA 99mTc-diethylacetanilide iminodiacetic acid
  • An object of the embodiments of the present application is to provide a detection device and a system including the detection device to solve at least one of the above problems.
  • an embodiment of the present application provides a detection device, including:
  • the processor is configured to process the electrical signal generated by the detector to determine the radioactivity of the target area.
  • the detector includes:
  • Scintillation crystal used to receive incident radioactive rays and generate corresponding optical signals
  • a photoelectric conversion device which is used to convert the optical signal generated by the scintillation crystal into an electrical signal
  • the coupling layer is used to couple the scintillation crystal and the photoelectric conversion device.
  • the scintillation crystal is a crystal array composed of multiple crystals or a whole continuous crystal.
  • the photoelectric conversion device includes one or more of a single photon avalanche diode, a photomultiplier tube, and a silicon photomultiplier.
  • the coupling layer is composed of optical silicone grease or optical glass.
  • the fixing structure includes a patch and / or a fixing glue, wherein the patch covers the outer surface of the detector, and the patch is provided with an electrical signal for outputting the detector Opening; the fixing glue is glued on the bottom of the detector.
  • the detection device further includes:
  • a collimator is used to collimate the incident direction of the radioactive rays and make the collimated radioactive rays enter the detector, the collimator is disposed between the detector and the fixed structure Furthermore, the fixing structure is fixed to the surface corresponding to the target area.
  • the collimator includes one or more collimating layers, each collimating layer is provided with one or more through holes, and when the collimator includes multiple collimating layers, there are at least two The alignment layers are coupled out of alignment.
  • the length of the collimator can be adjusted according to the position of the target area.
  • the detection device further includes:
  • the first wrapping layer is arranged around the scintillation crystal.
  • the first wrapping layer includes one of the following structures: a three-layer structure composed of barium sulfate, tin foil and shading tape, a two-layer structure composed of barium sulfate and tin foil, and a single layer composed of Teflon Structure, a two-layer structure composed of Teflon and shading tape, or a two-layer structure composed of Teflon and tin foil, wherein the barium sulfate or the Teflon is located in the innermost of the first wrapping layer Layer and attached to the outer surface of the scintillation crystal, the shading tape is located on the outermost layer of the first wrapping layer.
  • the detection device further includes:
  • the transmission structure is used to transmit the electrical signal generated by the detector to the processor, and it includes a wired transmission module and / or a wireless transmission module.
  • An embodiment of the present application further provides an imaging system, which includes the above-mentioned detection device and an image reconstruction device, the image reconstruction device is used for image reconstruction of the electrical signal generated by the detector in the detection device to A distribution image of the target area in the target organism is obtained.
  • the imaging system further includes:
  • An auxiliary device which is used together with the detection device, and includes one or more of a gamma camera, a flat PET, a flat SPECT, a PET complete machine, and a SPECT complete machine.
  • An embodiment of the present application also provides a method for detecting a living body by the above detection device, the method including:
  • Step S1 use the fixing structure to fix the detector on the outer surface corresponding to the target area in the target organism;
  • Step S2 use the detector to detect radioactive rays emitted from the target organism and generate corresponding electrical signals
  • Step S3 Use the processor to process the electrical signal generated by the detector to determine the radioactivity of the target area.
  • the method further includes:
  • step S0 the target area in the target organism is determined using the detector and the processor.
  • the method further includes:
  • a collimator is used to collimate the radioactive rays emitted from the target organism, and the collimated radioactive rays enter the detector.
  • the embodiments of the present application fix the detector to the surface corresponding to the target area in the living body by using a fixing structure without the need for a scanning rack and a ray tube, and the number of detectors is Compared with the PET or SPECT devices in the prior art, this can reduce the volume, reduce the cost, and simplify the structure, and can improve the mobility and adjustability of the detection device. Moreover, it can also improve the convenience of use of the detection device, and can monitor the biological situation in real time for 24 hours, and perform long-term time-phase imaging as required. Of patients, which improves its scope of application.
  • FIG. 1 is a schematic diagram of a three-dimensional separation structure of a detection device provided by an embodiment of the present application
  • FIG. 2 is a cross-sectional view of the detection device in FIG. 1;
  • FIG. 3 shows a schematic diagram of the detector on the skin surface of the human body
  • FIG. 4 shows a schematic diagram of the detector on the surface of the body cavity of the human body
  • Figure 5 is a schematic diagram of an animal experiment model
  • FIG. 6 shows the time-radioactivity curve corresponding to the animal experimental model in FIG. 5;
  • FIG. 7 is a schematic diagram of two collimated layers that are misaligned
  • FIGS. 1 and 2 are schematic structural diagrams of a system including the detection device in FIGS. 1 and 2 provided by an embodiment of the present application;
  • FIGS. 9 is a schematic flowchart of a method for detecting a living body using the detection device in FIGS. 1 and 2 according to an embodiment of the present application.
  • connection / coupling refers to the presence of features, steps or elements, but does not exclude the presence or addition of one or more other features, steps or elements.
  • connecting / or includes any and all combinations of one or more of the associated listed items.
  • radioactive rays may refer to X-rays, ⁇ -rays, ⁇ -rays, and / or ⁇ -rays.
  • the target organism may refer to an organism injected with a radiopharmaceutical (marked with a radionuclide), for example, a human or an animal, or other objects that need to be detected.
  • the target area may refer to an area where an abnormal organ (eg, heart, intestine, stomach, etc.) occurs within the organism, or may be another area of interest in the target organism that needs to be detected.
  • the surface corresponding to the target area may refer to the skin surface or body cavity surface of the living body.
  • the electrical signal may refer to an electrical pulse signal, a continuous electrical signal, or a discrete electrical signal.
  • the detection device the system including the detection device and the detection method provided by the embodiments of the present application will be described in detail below with reference to the drawings.
  • an embodiment of the present application provides a detection device 100, which may include:
  • the detector 110 is used to detect radioactive rays emitted from the target organism and generate corresponding electrical signals in response to the radioactive rays;
  • the fixing structure 120 is used to fix the detector 110 to the surface corresponding to the target area in the target organism;
  • the processor 130 is configured to process the electrical signal generated by the detector 110 to determine the radioactivity in the target area.
  • the detector 110 may include a scintillation crystal 111, a coupling layer 112, and a photoelectric conversion device 113 that are sequentially arranged from bottom to top.
  • the scintillation crystal 111 can be used to receive incident radioactive rays and generate corresponding optical signals (eg, visible light photons) after photoelectric effect, Compton effect, Rayleigh scattering, and / or electron pair effect and other effects occur.
  • the scintillation crystal 111 may include yttrium lutetium silicate (LYSO) crystal, lutetium silicate (LSO) crystal, bismuth germanate (BGO) crystal, barium fluoride (BaF2) crystal, lanthanum bromide (LaBr3) crystal, yttrium aluminate ( One or more of inorganic scintillation crystals such as YAP) crystals, lutetium aluminate (LuAP) crystals, sodium iodide (NaI) crystals, and cesium iodide (CsI) crystals.
  • LYSO yttrium lutetium silicate
  • LSO lutetium silicate
  • BGO bismuth germanate
  • BaF2 barium fluoride
  • LaBr3 lanthanum bromide
  • yttrium aluminate One or more of inorganic scintillation crystals such as YAP) crystals, lutet
  • the scintillation crystal 111 may be an entire row of crystals composed of a plurality of crystals that are completely cut or incompletely cut, or may be a whole continuous crystal.
  • the axial direction of the scintillation crystal 111 may be perpendicular to the surface corresponding to the target area, and it may be in contact with the surface during detection.
  • the coupling layer 112 may be used to couple the scintillation crystal 111 and the photoelectric conversion device 113 to couple the scintillation crystal 111 and the photoelectric conversion device 113 together.
  • the coupling layer 112 may be composed of a paste thickened with silicone oil (for example, optical silicone grease), or may be composed of optical glass, or may be other light guide structures.
  • the photoelectric conversion device 113 can be used to convert the optical signal generated by the scintillation crystal 111 into an electrical signal, which can be one or more of a single photon avalanche diode, photomultiplier tube, silicon photomultiplier, etc., or other Device with photomultiplier effect.
  • the detection device may include multiple detectors 110, and the number of detectors 110 is not limited herein.
  • the fixing structure 120 may be used to fix the detector 110 to the surface (eg, skin) corresponding to the target area in the target organism Surface or body cavity surface), as shown in Figures 3 and 4.
  • the fixing structure 120 may be detachably connected to the detector 110, and may be any structure that does not affect the penetration of radioactive rays and has a fixing effect, such as a patch 121, but is not limited thereto.
  • the application 121 can cover the outer surface of the detector 110 (specifically, it can refer to the outer surface of the photoelectric conversion device 113), and its surroundings or part of the area is directly attached to the surface corresponding to the target area or the periphery of the surface Thus, it can be ensured that the detector 110 is fixed on the surface corresponding to the target area in the target organism.
  • the patch 121 may be provided with an opening for the detector 110 (specifically, the photoelectric conversion device 113) to output an electrical signal to transmit the electrical signal generated by the detector 110 outward.
  • the fixing structure 120 may further include a fixing glue (for example, glue) 122, which may be adhered to the bottom of the detector 110 (specifically, may refer to the bottom of the scintillation crystal 111, that is, the side opposite to the photoelectric conversion device 113 ), It can also fix the detector 110 on the surface corresponding to the target area in the target organism, and can also be used to fill the gap between the scintillation crystal 111 and the skin surface of the target organism.
  • glue for example, glue
  • the processor 130 may be connected to the photoelectric conversion device 113 in the detector 110 so that the electrical signal output by the photoelectric conversion device 113 can be processed. Specifically, the processor 130 can record the number of electrical signals output by the photoelectric conversion device 113 per unit time, so that the radioactivity of the target area in the target organism can be determined according to the following formula (1):
  • Ci k * Counts, Counts, Counts, Counts, and Counts (1)
  • Ci radioactivity
  • Counts represents the number of electrical signals per unit time
  • k is a fixed parameter value.
  • the time-radioactivity curve can be drawn with time as the abscissa and the number of electrical signals as the ordinate, as shown in FIG. 6, which shows the time-radioactivity corresponding to the animal experiment model in FIG. 5. Degrees curve.
  • the metabolic law of the target area can be determined, so as to determine whether the target area is diseased.
  • the location of the lesion and / or the type of disease can be comprehensively judged. For example, for the case where the target area is the human intestine, the radioactivity starts to appear within about 15 minutes under normal circumstances, and the radioactivity reaches the peak within 1 hour and enters the overall decline stage.
  • the time-radioactivity curve obtained after processing by the processor 130 shows that the radioactivity does not reach the peak within 1 hour, it means that the patient may have biliary obstruction, and the biliary tract can be determined according to the time when the radioactivity reaches the peak The degree of obstruction.
  • the target area is the human heart
  • the time-radioactivity curve obtained after processing by the processor 130 shows that the radioactivity has not reached the peak value or even the radioactivity is missing within the preset time, it means that the patient may have Myocardial infarction, and the severity of infarction can be determined according to the time when the radioactivity reaches its peak.
  • the processor 130 may also perform amplification, integration, analog-to-digital conversion and other processing on the electrical signals to convert the electrical signals into digital Signal to facilitate subsequent data processing.
  • processor 130 may be a processor in a computer, the entire computer, or other computing devices.
  • the detection device 100 may further include a collimator 140 matched with the detector 110, which may be used to collimate and collimate the radioactive rays emitted from the target organism After the radioactive rays enter the detector 110, this can ensure that the radioactive rays received by the detector 110 come from the opposite straight position, thereby avoiding interference caused by other signals around the target organism and in the body, which can improve subsequent detection results The pertinence of this can further improve the accuracy of subsequent diagnosis results.
  • a collimator 140 matched with the detector 110, which may be used to collimate and collimate the radioactive rays emitted from the target organism After the radioactive rays enter the detector 110, this can ensure that the radioactive rays received by the detector 110 come from the opposite straight position, thereby avoiding interference caused by other signals around the target organism and in the body, which can improve subsequent detection results The pertinence of this can further improve the accuracy of subsequent diagnosis results.
  • the collimator 140 may be disposed between the detector 110 and the solid structure 120, specifically between the scintillation crystal 111 and the application 121, and preferably, it may be perpendicular to the surface corresponding to the target area. Moreover, the collimator 140 may be fixed to the surface corresponding to the target area in the target organism together with the detector 110 through the fixing structure 120. The collimator 140 and the detector 110 may be fixed or relatively moved. Moreover, the collimator 140 may cover at least two side surfaces of the scintillation crystal 111 and another surface opposite to the receiving surface (ie, the surface that receives photons, for example, the bottom surface), and may also cover the coupling layer 112 and the photoelectric Conversion crystal 113.
  • the scintillation crystal 111 in the detector 110 may directly contact the surface corresponding to the target area at the bottom end of the collimator 140; when the fixing structure 120 includes the fixing glue 122 The scintillation crystal 111 in the detector 110 can be in indirect contact with the surface corresponding to the target area at the bottom end of the collimator 140 through the fixing glue 122.
  • an opening corresponding to the opening in the applicator 121 may be provided on the top of the collimator 140, and the electrical signal generated by the detector 110 may be output through the opening.
  • the collimator 140 may include one or more collimating layers, each collimating layer is provided with one or more through holes, the direction of each through hole is directed to the scintillation crystal 111 in the detector 110, and the through hole may be Circle, triangle, polygon and other shapes.
  • the misalignment coupling may mean that the center lines of the through holes of the two collimating layers do not coincide when they are coupled in series, as shown in FIG. 7.
  • the collimator 140 may be composed of tungsten steel or wrapped lead and other radiation protection materials. Through the collimator 140, interference of other rays around the target organism can be avoided, so that the accuracy of subsequent detection results can be further improved, thereby facilitating diagnosis of the disease of the organism.
  • the length of the collimator 140 can be adjusted according to the position of the target area, so that it can be used flexibly. For example, if the target area is part of myocardium, the length of collimator 140 is longer to shield all other signals around the target organism and in the body; if the target area is the entire intestine, the length of collimator 140 It can be significantly shorter than when the target area is part of myocardium to improve the patient's experience.
  • collimator 140 may actually be located between the detector 110 and the solid glue 122.
  • the detection device 100 may further include a first cladding layer 150, which may be disposed around the scintillation crystal 111 to reflect the visible light photons generated inside the scintillation crystal 111 and protect the scintillation crystal 111 from The external visible light signal can be bonded to the fixing glue 122 to fix the scintillation crystal 111.
  • the first cladding layer 150 may be a single-layer or multi-layer structure to improve the protection effect of the scintillation crystal 111.
  • the wrapping layer 150 may be a three-layer structure composed of barium sulfate, tin foil and shading tape, a two-layer structure composed of barium sulfate and tin foil, etc., a single-layer structure composed of Teflon, a Teflon and shading A two-layer structure composed of tape or the like, or a two-layer structure composed of Teflon and tin foil, etc., where barium sulfate and Teflon may be located in the innermost layer of the first wrapping layer 150 and attached to the scintillation crystal 111
  • the outer surface; tin foil can be located in the middle layer of the first wrapping layer 150, and can be used to wrap barium sulfate and Teflon; shading tape can be located in the outermost layer of the first wrapping layer 150.
  • the detection device 100 may further include a transmission structure 160, which is connected to the detector 110 and the processor 130, and may be used to connect the electricity generated by the photoelectric conversion device 113 in the detector 110
  • the signal is transmitted to the processor 130.
  • the transmission structure may include a wired transmission module and / or a wireless transmission module, wherein the wired transmission module may be a data transmission line or a cable, etc.
  • the wireless transmission module may be through wireless routing, WiFi protocol, Zigbee protocol, etc.
  • the electrical signal is transmitted to the processor 130 for subsequent processing. Through the transmission structure 160, the electrical signal generated by the detector 110 can be flexibly transmitted, so as to meet different application requirements.
  • the detection device 100 may further include a memory (not shown in the figure), which may be connected to the processor 130 to store the data processing result obtained by the processor 130, and it may also The photoelectric conversion device 113 in the detector 110 is connected to store the electrical signal generated by the photoelectric conversion device 113.
  • the detection device 100 may further include a second wrapping layer (not shown in the figure), which may be used to wrap the structure of the detector 110 and the collimator 140 in order to facilitate Fix it to the surface of the body cavity.
  • the second cladding layer may be composed of a material that does not affect the penetration of radioactive rays and can be placed in a living body.
  • the detection device fixes the detector to the surface corresponding to the target area in the living body by using a fixing structure, without requiring a scanning rack and a ray tube, and the number of detectors
  • the PET or SPECT devices in the prior art are significantly reduced, which can achieve the purposes of reducing the volume, reducing the cost, and simplifying the structure, and can improve the mobility and adjustability of the detection device.
  • the detector is fixed on the living body without the need for a scanning rack, the living body can be monitored anytime, anywhere, which can improve the convenience of use of the detection device, and can monitor the living body situation in real time 24 hours, according to demand Longer time-phase imaging can also be applied to patients with claustrophobia, hyperactivity, and inability to lie supine, which improves its scope of application.
  • the detector after the detector generates electrical signals, the number of electrical signals per unit time can be quickly recorded to determine the radioactivity of the target area without subsequent image reconstruction, which can reduce power consumption and increase data processing speed.
  • An embodiment of the present application also provides a system including the detection device 100 described in the foregoing embodiment, as shown in FIG. 8.
  • the system may further include an image reconstruction device 200, which may be connected to the photoelectric conversion device 113 and / or the processor 130 in the detector 110, and may be used to generate electricity from the detector 110 in the detection device 100.
  • the signal is reconstructed to obtain a distribution image of the target area in the target organism. According to the distribution image, it can be more conducive to determine the metabolic law of the birth object for subsequent scientific research, and it can also help the doctor to intuitively diagnose the diseased parts and types in the living body, so that symptomatic treatment can be performed.
  • image reconstruction device 200 may be integrated with the processor 130 or set independently.
  • the system may also include an auxiliary device (not shown in the figure), which may be used together with the detection device 100.
  • an auxiliary device (not shown in the figure), which may be used together with the detection device 100.
  • the detection device 110 and / or the auxiliary device may be selected to be used to further ensure the accuracy of subsequent analysis or diagnosis results.
  • the auxiliary device may be a gamma camera, a flat PET, a flat SPECT, a PET complete machine or a SPECT complete machine in the prior art.
  • An embodiment of the present application also provides a method for detecting a living body using the above detection device. As shown in FIG. 9, the method may include the following steps:
  • Step S1 Fix the detector on the surface corresponding to the target area in the target organism by using a fixed structure.
  • the fixing structure may be used to fix the detector to the skin surface or body cavity surface corresponding to the target area in the target organism.
  • Step S2 Use the detector to detect the radioactive rays emitted from the target organism and generate corresponding electrical signals.
  • the detector After the detector is fixed to the target organism, the detector can be used to detect the radioactive rays emitted from the target organism. After detecting radioactive rays, the detector will generate a corresponding electrical signal.
  • Step S3 Use the processor to process the electrical signal generated by the detector to determine the radioactivity in the target area.
  • the processor can be used to record the number of electrical signals generated by the detector 110 per unit time, and then calculate the radioactivity in the target area according to the above formula (1). Furthermore, the time-radioactivity curve can be plotted with time as the abscissa and the number of electrical signals as the ordinate. According to the determined radioactivity or the drawn time-radioactivity curve, the metabolic law of the birth object, the lesion location and / or the type of disease can be determined.
  • the method may further include:
  • Step S0 use the detector and the processor to determine the target area in the target organism
  • the area to be detected in the target organisms can be preliminarily determined based on the doctor ’s preliminary diagnosis of the target organisms or previous statistical empirical data, and then based on the area to be detected and used Detector and processor to determine the target area. specifically,
  • the detector Place the detector on the surface of the skin or body cavity corresponding to the area to be detected, and then use the detector to detect the radioactive rays emitted from the living body and generate the corresponding electrical signal and move the detector around the area to be detected, using the processor to The electrical signal generated by the detector is processed to determine the position corresponding to the maximum radioactivity, thereby determining the position as the target area.
  • the movement of the detector can be controlled by a person or a controller.
  • the target area may refer to an area where an abnormal organ (eg, heart, intestine, stomach, etc.) occurs inside the organism, or may be another area in the target organism that needs to be detected.
  • the method may further include:
  • Step S4 collimate the radioactive rays emitted from the target organism using a collimator, and make the collimated radioactive rays enter the detector.
  • the detector Before using the detector to detect the radioactive rays of the target organism, you can use a collimator to collimate the radioactive rays, and then use the detector to detect the collimated radioactive rays to avoid other signal bands around the target organism and in the body Interference.
  • the embodiments of the present application fix the detector to the surface corresponding to the target area in the target organism by using the fixing structure, and use the detector to detect the radiation emitted from the target organism and record the detection using the processor
  • the number of electrical signals generated by the device determines the radioactivity of the target area without image reconstruction, which can reduce power consumption and increase data processing speed.

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Abstract

探测装置（100）、包括探测装置（100）的成像系统及其探测方法，探测装置（100）包括：探测器（110），用于探测从目标生物体发出的放射性射线并响应于放射性射线而产生对应的电信号；固定结构（120），用于将探测器（110）固定于目标生物体中的目标区域所对应的表面；处理器（130），用于对探测器（110）产生的电信号进行处理以确定出目标区域的放射性活度。通过利用本技术方案，可以降低成本、减小功耗、提高数据处理速度并为科研及临床提供新的影像学依据。

Description

探测装置、包括该探测装置的成像系统及其探测方法 技术领域
本申请涉及辐射探测应用领域，特别涉及一种探测装置、包括该探测装置的成像系统及其探测方法。
背景技术
本部分的描述仅提供与本申请公开相关的背景信息，而不构成现有技术。
核医学成像是一种现代医学影像技术，其通过向人体注入标记有能产生γ光子或正电子的放射性核素的示踪剂，并通过在人体外探测放射性核素所产生的射线来获知示踪剂在人体内的分布及变化信息，从而用于疾病的诊断和治疗。核医学成像是典型的分子影像手段，其能够反映人体内的生理、代谢、功能、分子信息，是当前主流医学影像手段之一。
核医学成像技术主要包括正电子发射断层成像(Positron Emission Tomography，简称PET)和单光子发射计算机断层成像(Single Photon Emission Computed Tomography，简称SPECT)这两种技术。其中，PET技术和SPECT技术分别主要是探测标记有发射正电子和单光子的放射性核素的药物在人体内的分布及变化信息。
现有技术中在利用PET装置或SPECT装置等装置来对人体进行探测以辅助疾病诊断时，通常是将放射性核素标记的药物注射到人体，然后利用装置内的探测器围绕人体，从不同角度采集人体内的药物所产生的光信号，将所采集的光信号转换为电信号并且对电信号进行图像重建，从而可以根据所得到的重建图像来确定出人体内的病变部位以及病变类型。例如，可以利用SPECT成像装置对婴儿进行99mTc-二乙基乙酰苯胺亚氨二醋酸(EHIDA)肝胆动态显像，从而可以检测出婴儿是否患有先天性胆道闭锁。
发明内容
在实现本申请过程中，发明人发现现有技术中的PET装置和SPECT装置至少存在如下问题：
(1)具有射线管、扫描架、大量探测器等器件，这导致其成本较高、体积较大、结构复杂，并且其移动性和可调性较差；
(2)在利用上述装置对人体进行检查时，无法24小时实时监测人体情况，并且无法按需求进行较长时间的时相显像；
(3)由于上述装置的封闭性而不适用于幽闭恐惧、多动症、端坐呼吸、无法平卧的患者等，从而影响了其适用范围；
(4)在采集所有的信号之后需要进行图像重建以得到人体内部的三维分布图像，这使得从上述装置得到具有参考价值的临床数据所需时间较长，无法实时做出诊断；
本申请实施例的目的是提供一种探测装置、包括该探测装置的系统，以解决上述至少一个问题。
为了实现上述目的，本申请实施例提供了一种探测装置，其包括：
探测器，用于探测从目标生物体发出的放射性射线并响应于所述放射性射线而产生对应的电信号；
固定结构，用于将所述探测器固定于所述目标生物体中的目标区域所对应的表面；
处理器，用于对所述探测器产生的电信号进行处理以确定出所述目标区域的放射性活度。
优选地，所述探测器包括：
闪烁晶体，用于接收入射的放射性射线并产生对应的光信号；
光电转换器件，用于将所述闪烁晶体产生的光信号转换为电信号；
耦合层，用于耦合所述闪烁晶体和所述光电转换器件。
优选地，所述闪烁晶体为由多个晶体构成的晶体阵列或整块连续晶体。
优选地，所述光电转换器件包括单光子雪崩二极管、光电倍增管和硅光电倍增器中的一种或多种。
优选地，所述耦合层由光学硅脂或光学玻璃组成。
优选地，所述固定结构包括敷贴和/或固定胶，其中，所述敷贴包覆所述探测器的外表面，并且所述敷贴上设有用于输出所述探测器产生的电信号的开口；所述固定胶粘接在所述探测器的底部上。
优选地，所述探测装置还包括：
准直器，用于将所述放射性射线的入射方向进行准直，并使准直后的放射性射线进入所述探测器，所述准直器设置在所述探测器与所述固定结构之间并且通过所述固定结构而固定于所述目标区域所对应的表面。
优选地，所述准直器包括一个或多个准直层，每个准直层上设有一个或多个通孔，并且当所述准直器包括多个准直层时，至少有两个准直层之间是错位耦合的。
优选地，所述准直器的长度可根据所述目标区域的位置来调节。
优选地，所述探测装置还包括：
第一包裹层，设置于所述闪烁晶体的周围。
优选地，所述第一包裹层包括以下结构中的一种：由硫酸钡、锡纸以及遮光胶带组成的三层结构、由硫酸钡和锡纸组成的两层结构、由特氟龙组成的单层结构、由特氟龙和遮光胶带组成的两层结构、或者由特氟龙和锡纸组成的两层结构，其中，所述硫酸钡或所述特氟龙位于所述第一包裹层的最内层并且贴附于所述闪烁晶体的外表面，所述遮光胶带位于所述第一包裹层的最外层。
优选地，所述探测装置还包括：
传输结构，用于将所述探测器产生的电信号传输至所述处理器，并且其包括有线传输模块和/或无线传输模块。
本申请实施例还提供了一种成像系统，其包括：上述探测装置以及图像重建装置，所述图像重建装置用于对所述探测装置中的所述探测器所产生的电信号进行图像重建以得到所述目标生物体内的所述目标区域的分布图像。
优选地，所述成像系统还包括：
辅助装置，其与所述探测装置一起配合使用，并且包括γ照相机、平板PET、平板SPECT、PET整机和SPECT整机中的一种或多种。
本申请实施例还提供了一种上述探测装置对生物体进行探测的方法，所述方法包括：
步骤S1：利用固定结构将探测器固定在目标生物体中的目标区域所对应的外表面；
步骤S2：利用所述探测器探测从所述目标生物体发出的放射性射线并产生对应的电信号；
步骤S3：利用处理器对所述探测器所产生的电信号进行处理以确定出所述目标区域的放射性活度。
优选地，在步骤S1之前，所述方法还包括：
步骤S0，利用所述探测器和所述处理器确定所述目标生物体中的所述目标区域。
优选地，在步骤S2之前，所述方法还包括：
利用准直器对从所述目标生物体发出的所述放射性射线进行准直，并使准直后的所述放射性射线进入所述探测器。
由以上本申请实施例提供的技术方案可见，本申请实施例通过利用固定结构将探测器固定于生物体中的目标区域所对应的表面，而不需要扫描架和射线管，并且探测器数量相比现有技术中的PET或SPECT装置明显减少，这可以实现减小体积、降低成本以及简化结构的目的，并且可以提高探测装置的移动性和可调性。而且，还可以提高探测装置的使用便利性，并且可以24小时实时监测生物体情况，按需求进行较长时间的时相显像，还可以适用于幽闭 恐惧、多动症、端坐呼吸、无法平卧的患者，这提高了其适用范围。
附图说明
为了更清楚地说明本申请实施例或现有技术中的技术方案，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申请中记载的一些实施例，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是本申请实施例提供的一种探测装置的三维立体拆分结构的示意图；
图2是图1中的探测装置的剖视图；
图3示出了探测器在人体的皮肤表面的示意图；
图4示出了探测器在人体的体腔表面的示意图；
图5为动物实验模型的示意图；
图6示出了图5中的动物实验模型所对应的时间-放射性活度曲线；
图7为错位耦合的两个准直层的示意图；
图8是本申请实施例提供的一种包括图1和图2中的探测装置的系统的结构示意图；
图9是本申请实施例提供的一种利用图1和图2中的探测装置对生物体进行探测的方法的流程示意图。
具体实施方式
下面将结合本申请实施例中的附图，对本申请实施例中的技术方案进行清楚、完整地描述，显然，所描述的实施例仅仅是用于解释说明本申请的一部分实施例，而不是全部的实施例，并不希望限制本申请的范围或权利要求书。基于本申请中的实施例，本领域普通技术人员在没有做出创造性劳动的前提下所获得的所有其它实施例，都应当属于本申请保护的范围。
需要说明的是，当元件被称为“设置在”另一个元件上，它可以直接设置在另一个元件上或者也可以存在居中的元件。当元件被称为“连接/耦合”至另一个元件，它可以是直接连接/耦合至另一个元件或者可能同时存在居中元件。本文所使用的术语“连接/耦合”可以包括电气和/或机械物理连接/耦合。本文所使用的术语“包括/包含”指特征、步骤或元件的存在，但并不排除一个或更多个其它特征、步骤或元件的存在或添加。本文所使用的术语“和/或”包括一个或多个相关所列项目的任意的和所有的组合。
除非另有定义，本文所使用的所有的技术和科学术语与属于本申请的技术领域的技术人 员通常理解的含义相同。本文中所使用的术语只是为了描述具体实施例的目的，而并不是旨在限制本申请。
另外，在本申请的描述中，术语“第一”、“第二”等仅用于描述目的和区别类似的生物，两者之间并不存在先后顺序，也不能理解为指示或暗示相对重要性。此外，在本申请的描述中，除非另有说明，“多个”的含义是两个或两个以上。
在本申请的实施例中，放射性射线可以是指X射线、γ射线、β射线和/或α射线等。目标生物体可以是指注射有放射性药物(其上标记有放射性核素)的生物体，例如，人或动物，也可以是其它需要检测的对象。目标区域可以是指生物体内部出现异常的器官(例如，心脏、肠道、胃部等)所在区域，也可以是目标生物体中需要检测的其它感兴趣区域。目标区域所对应的表面可以是指生物体的皮肤表面或体腔表面。电信号可以是指电脉冲信号、连续电信号或离散电信号等。
下面结合附图对本申请实施例所提供的探测装置、包括该探测装置的系统及其探测方法进行详细说明。
如图1和图2所示，本申请实施例提供了一种探测装置100，其可以包括：
探测器110，用于探测从目标生物体发出的放射性射线并响应于放射性射线而产生对应的电信号；
固定结构120，用于将探测器110固定于目标生物体中的目标区域所对应的表面；
处理器130，用于对探测器110产生的电信号进行处理，以确定出目标区域的放射性活度。
在本申请的实施例中，探测器110可以包括从下到上依次设置的闪烁晶体111、耦合层112以及光电转换器件113。闪烁晶体111可以用于接收入射的放射性射线并在发生光电效应、康普顿效应、瑞利散射和/或电子对效应等效应后而产生对应的光信号(例如，可见光光子)。闪烁晶体111可以包括硅酸钇镥(LYSO)晶体、硅酸镥(LSO)晶体、锗酸铋(BGO)晶体、氟化钡(BaF2)晶体、溴化镧(LaBr3)晶体、铝酸钇(YAP)晶体、铝酸镥(LuAP)晶体、碘化钠(NaI)晶体、碘化铯(CsI)晶体等无机闪烁晶体中的一种或多种。闪烁晶体111可以是完全切割或不完全切割的多个晶体构成的晶体整列，也可以是整块连续晶体。闪烁晶体111的轴向可以与目标区域所对应的表面垂直，并且在探测时其可以与所述表面接触。耦合层112可以用于耦合闪烁晶体111和光电转换器件113，以实现将闪烁晶体111和光电转换器件113联接在一起。耦合层112可以是由硅油稠化而成的膏状物(例如，光学硅脂)组成的，也可以是由光学玻璃组成，还可以是其它光导结构。光电转换器件113可以用于将闪烁晶体111产生的光信号转换为电信号，其可以是单光子雪崩二极管、光电倍增管和硅光电倍增器等中的一种或多种，也可以是其它的具有光电倍增效应的器件。
需要说明的是，虽然附图中仅示出了一个探测器110，但实际上该探测装置可以包括多个探测器110，本文对探测器110的数量并没有限制。
在本申请的实施例中，在实际操作中确定出目标生物体中的目标区域之后，固定结构120可以用于将探测器110固定在目标生物体中的目标区域所对应的表面(例如，皮肤表面或体腔表面)处，如图3和图4所示。固定结构120可以与探测器110可拆卸连接，并且可以是不影响放射性射线穿透并且具有固定作用的任何结构，例如可以是敷贴121，但不限于此。敷贴121可以包覆探测器110的外表面(具体地，可以是指光电转换器件113的外表面)，并且其四周或部分区域与目标区域所对应的表面或所述表面的外围直接贴合，从而可以保证将探测器110固定在目标生物体中的目标区域所对应的表面。另外，敷贴121上可以设有供探测器110(具体地，光电转换器件113)输出电信号的开口，以向外传输探测器110所产生的电信号。
此外，固定结构120还可以包括固定胶(例如，胶水)122，其可以粘接在探测器110的底部(具体地，可以是指闪烁晶体111的底部，即与光电转换器件113相对的一侧)上，其也可以将探测器110固定在目标生物体中的目标区域所对应的表面，还可以用于填充闪烁晶体111与目标生物体的皮肤表面之间的空隙。在固定结构120包括敷贴121和固定胶122时，可以使得探测器110的固定效果更好。
在本申请的实施例中，处理器130可以与探测器110中的光电转换器件113连接，从而可以对光电转换器件113输出的电信号进行处理。具体地，处理器130可以记录单位时间内光电转换器件113输出的电信号的数量，从而可以根据以下公式(1)来确定目标生物体中的目标区域的放射性活度：
Ci＝k*Counts                                           (1)
其中，Ci表示放射性活度；Counts表示单位时间内的电信号数量；k为固定的参数值。
而且，可以以时间为横坐标、电信号数量为纵坐标，绘制时间-放射性活度曲线，如图6所示，图6示出的是图5中的动物实验模型所对应的时间-放射性活度曲线。根据所确定的放射性活度或者所绘制的时间-放射性活度曲线，便可以确定出目标区域的代谢规律，从而可以判断目标区域是否病变。通过根据不同位置的探测器的电信号来确定的放射性活度，可以综合判断出病变位置和/或疾病类型等。例如，对于目标区域为人体肠道的情形，正常情况下约15min内放射性活度开始出现，1小时内放射性活度达到峰值并进入整体下降阶段。如果处理器130处理后所得到的时间-放射性活度曲线显示出1小时内放射性活度未达到峰值，则说明该病人可能患有胆道梗阻，并且可以根据放射性活度达到峰值的时间来确定胆道梗阻程度。再例如，对于目标区域为人体心脏的情形，如果处理器130处理后所得到的时间-放射性活度曲线显示出预设时间内放射性活度未达到峰值甚至放射性缺失，则说明该病人可能患有心肌梗 死，并且可以根据放射性活度达到峰值的时间来确定梗死严重程度。
在本申请的另一实施例中，在记录光电转换器件113输出的电信号的数量之前，处理器130还可以对电信号进行放大、积分、模数转换等处理，以将电信号转换为数字信号，从而便于后续数据处理。
需要说明的是，处理器130可以是计算机中的处理器，也可以是整个计算机，还可以其它的计算设备。
在本申请的另一实施例中，该探测装置100还可以包括与探测器110匹配设置的准直器140，其可以用于将从目标生物体发出的放射性射线进行准直，并使准直后的放射性射线进入探测器110，这可以保证探测器110接收的放射性射线来自于其所对的直线位置，从而可以避免目标生物体周围及体内其它信号带来的干扰，这可以提高后续探测结果的针对性，进而可以提高后续诊断结果的准确性。
准直器140可以设置在探测器110与固体结构120之间，具体地可以设置在闪烁晶体111与敷贴121之间，并且优选地，其可以垂直于所述目标区域所对应的表面。而且，准直器140可以通过固定结构120而与探测器110一起固定于目标生物体中的目标区域所对应的表面。准直器140与探测器110之间可以是固定的，也可以相对移动。而且，准直器140可以至少包覆闪烁晶体111的两个侧面以及与接收面(即，接收到光子的表面，例如，底面)相对的另一个表面，并且还可以包覆耦合层112以及光电转换晶体113。另外，在固定结构120不包括固定胶122时，探测器110中的闪烁晶体111可以在准直器140的底端处与目标区域所对应的表面直接接触；在固定结构120包括固定胶122时，探测器110中的闪烁晶体111可以通过固定胶122而在准直器140的底端处与目标区域所对应的表面间接接触。
在固定结构包括敷贴121时，准直器140的顶端上可以设有与敷贴121上的开口对应的开口，通过该开口，可以向外输出探测器110所产生的电信号。
准直器140可以包括一个或多个准直层，每个准直层上设有一个或多个通孔，每个通孔的方向指向探测器110中的闪烁晶体111，并且通孔可以是圆形、三角形、多边形等形状。另外，当所述准直层为多个时，其中至少有两个准直层之间是错位耦合的，并且准直层的位置是可调整的，从而可以提高准直器140的性能并且可以满足不同的应用需求。所述错位耦合可以是指两个准直层在串联耦合时两者的通孔的中心线不重合，如图7所示。
准直器140可以由钨钢或包裹后的铅等防辐射材料组成。通过准直器140，可以避免目标生物体周围其它射线的干扰，从而可以进一步提高后续探测结果的准确性，进而有利于对生物体的疾病诊断。
另外，准直器140的长度可以根据目标区域的位置来进行调节，从而可以灵活使用。例 如，如果所述目标区域为部分心肌，则准直器140的长度较长，以屏蔽目标生物体周围及体内其他所有信号；如果所述目标区域为整个肠道，则准直器140的长度可以明显小于目标区域为部分心肌时的长度，以提高患者的体验效果。
需要说明的是，虽然图中仅示出了准直器140位于探测器110与敷贴121之间，但实际上准直器140也可以位于探测器110与固体胶122之间。
在本申请的另一实施例中，该探测装置100还可以包括第一包裹层150，其可以设置于闪烁晶体111的周围，以反射闪烁晶体111内部产生的可见光光子，保护闪烁晶体111不受外界可见光信号的影响，并且可以与固定胶122粘接以实现对闪烁晶体111的固定。第一包裹层150可以是单层或多层结构，以提高对闪烁晶体111的保护效果。例如，包裹层150可以是由硫酸钡、锡纸以及遮光胶带等组成的三层结构、由硫酸钡和锡纸等组成的两层结构、由特氟龙组成的单层结构、由特氟龙和遮光胶带等组成的两层结构、或者由特氟龙和锡纸等组成的两层结构，其中，硫酸钡和特氟龙可以位于第一包裹层150的最内层，并且贴附于闪烁晶体111的外表面；锡纸可以位于第一包裹层150的中间层，并且可以用于包裹硫酸钡和特氟龙；遮光胶带可以位于第一包裹层150的最外层。
在本申请的另一实施例中，该探测装置100还可以包括传输结构160，其与探测器110和处理器130连接，其可以用于将探测器110中的光电转换器件113所产生的电信号传输给处理器130。所述传输结构可以包括有线传输模块和/或无线传输模块，其中，有线传输模块可以是数据传输线或电缆等，所述无线传输模块可以通过无线路由、WiFi协议、紫蜂(Zigbee)协议等方式将电信号传输至处理器130以进行后续处理。通过传输结构160，可以灵活地传输探测器110所产生的电信号，从而可以满足不同的应用需求。
在本申请的另一实施例中，该探测装置100还可以包括存储器(图中未示出)，其可以与处理器130连接，以存储处理器130所得到的数据处理结果，并且其还可以与探测器110中的光电转换器件113连接，以存储光电转换器件113所产生的电信号。
在本申请的另一实施例中，该探测装置100还可以包括第二包裹层(图中未示出)，其可以用于将探测器110和准直器140等结构包裹在其中，以便于将其固定于体腔表面。所述第二包裹层可以由不影响放射性射线穿透并且可以置于生物体内的材料组成。
通过以上描述可以看出，本申请实施例提供的探测装置通过利用固定结构将探测器固定于生物体中的目标区域所对应的表面，而不需要扫描架和射线管，并且探测器数量相比现有技术中的PET或SPECT装置明显减少，这可以实现减小体积、降低成本以及简化结构的目的，并且可以提高探测装置的移动性和可调性。而且，由于探测器固定于生物体上，而不需要扫描架，所以可以随时随地对生物体进行监测，这可以提高探测装置的使用便利性，并且可以 24小时实时监测生物体情况，按需求进行较长时间的时相显像，还可以适用于幽闭恐惧、多动症、无法平卧的患者，这提高了其适用范围。另外，在探测器产生电信号之后，可快速记录单位时间内的电信号的数量以确定出目标区域的放射性活度，而不需要进行后续图像重建，这可以减少功耗并且提高数据处理速度。
本申请实施例还提供了一种包括上述实施例中描述的探测装置100的系统，如图8所示。该系统还可以包括图像重建装置200，图像重建装置200可以与探测器110中的光电转换器件113和/或处理器130连接，并且可以用于对探测装置100中的探测器110所产生的电信号进行图像重建以得到目标生物体内的目标区域的分布图像。根据该分布图像，可以更有利于确定出生物体的代谢规律以便于后续科学研究，也可以有利于医生直观地诊断出生物体内的病变部位及其类型，从而可以对症治疗。
需要说明的是，图像重建装置200可以与处理器130集成于一体或者独立设置。
另外，在本申请的另一实施例中，该系统也还可以包括辅助装置(图中未示出)，其可以与探测装置100一起配合使用。针对不同的生物体、同一生物体的不同部位以及生物体的当前状况，可以选择使用探测装置110和/或辅助装置，从而可以更进一步保证后续分析或诊断结果的准确性。该辅助装置可以是现有技术中的γ照相机、平板PET、平板SPECT、PET整机或SPECT整机。
本申请实施例还提供了一种利用上述探测装置对生物体进行探测的方法，如图9所示，该方法可以包括以下步骤：
步骤S1：利用固定结构将探测器固定在目标生物体中的目标区域所对应的表面。
在预先确定出目标生物体中的目标区域之后，可以利用固定结构将探测器固定在目标生物体中的目标区域所对应的皮肤表面或体腔表面。
步骤S2：利用探测器探测从目标生物体发出的放射性射线并产生对应的电信号。
在将探测器固定于目标生物体之后，可以利用探测器来探测从目标生物体发出的放射性射线。在探测到放射性射线之后，探测器会产生对应的电信号。
步骤S3：利用处理器对探测器所产生的电信号进行处理以确定出目标区域的放射性活度。
在探测器产生电信号之后，可以利用处理器记录单位时间内探测器110所产生的电信号的数量，然后根据上述公式(1)来计算目标区域的放射性活度。而且，可以以时间为横坐标、电信号数量为纵坐标，绘制时间-放射性活度曲线。根据所确定的放射性活度或者所绘制的时间-放射性活度曲线，便可以确定出生物体的代谢规律、病变部位和/或疾病类型等。
在本申请的另一实施例中，在步骤S1之前，该方法还可以包括：
步骤S0：利用探测器和处理器确定目标生物体中的目标区域；
在对注射有放射性药物的目标生物体进行探测时，可以根据医生对目标生物体的初步诊断结果或者之前统计的经验数据来初步确定目标生物体中的待探测区域，然后根据待探测区域并利用探测器和处理器来确定目标区域。具体地，
将探测器置于待探测区域所对应的皮肤表面或体腔表面，然后利用探测器探测从生物体内发出的放射性射线并产生对应的电信号并且在待探测区域附近左右移动探测器，利用处理器对探测器所产生的电信号进行处理，以确定出放射性活度最大时所对应的位置，从而将该位置确定为目标区域。
所述探测器的移动可以由人或控制器来控制。所述目标区域可以是指生物体内部出现异常的器官(例如，心脏、肠道、胃部等)所在区域，也可以是目标生物体中需要检测的其它区域。
在本申请中的另一实施例中，在步骤S0或S2之前，该方法还可以包括：
步骤S4：利用准直器对从目标生物体发出的放射性射线进行准直，并使准直后的放射性射线进入探测器。
在利用探测器探测目标生物体的放射性射线之前，可以利用准直器来对放射性射线进行准直，然后利用探测器探测准直后的放射性射线，以避免目标生物体周围及其体内其它信号带来的干扰。
关于上述步骤S0-S4的详细描述，可以参照上述对探测装置的描述，在此不再赘叙。
通过上述描述可以看出，本申请实施例通过利用固定结构将探测器固定于目标生物体中的目标区域所对应的表面，并且利用探测器探测从目标生物体发出的射线以及利用处理器记录探测器所产生的电信号的数量以确定出目标区域的放射性活度，而不需要进行图像重建，这可以减少功耗并且提高数据处理速度。
上述实施例阐明的系统、装置、单元、模块等，具体可以由计算机芯片和/或实体实现，或者由具有某种功能的产品来实现。为了描述的方便，描述以上装置时以功能分为各种器件分别描述。当然，在实施本申请时可以把各器件的功能在同一个或多个计算机芯片和/或实体中实现。
虽然本申请提供了如上述实施例或流程图所述的方法操作步骤，但基于常规或者无需创造性的劳动在所述方法中可以包括更多或者更少的操作步骤。在逻辑性上不存在必要因果关系的步骤中，这些步骤的执行顺序不限于本申请实施例提供的执行顺序。
本说明书中的各个实施例均采用递进的方式描述，各个实施例之间相同相似的部分互相 参见即可，每个实施例重点说明的都是与其它实施例的不同之处。
上述实施例是为便于该技术领域的普通技术人员能够理解和使用本申请而描述的。熟悉本领域技术的人员显然可以容易地对这些实施例做出各种修改，并把在此说明的一般原理应用到其它实施例中而不必经过创造性的劳动。因此，本申请不限于上述实施例，本领域技术人员根据本申请的揭示，不脱离本申请范畴所做出的改进和修改都应该在本申请的保护范围之内。

Claims (17)

  1. 一种探测装置，其特征在于，所述探测装置包括：
    探测器，用于探测从目标生物体发出的放射性射线并响应于所述放射性射线而产生对应的电信号；
    固定结构，用于将所述探测器固定于所述目标生物体中的目标区域所对应的表面；
    处理器，用于对所述探测器产生的电信号进行处理以确定出所述目标区域的放射性活度。
  2. 根据权利要求1所述的探测装置，其特征在于，所述探测器包括：
    闪烁晶体，用于接收入射的放射性射线并产生对应的光信号；
    光电转换器件，用于将所述闪烁晶体产生的光信号转换为电信号；
    耦合层，用于耦合所述闪烁晶体和所述光电转换器件。
  3. 根据权利要求2所述的探测装置，其特征在于，所述闪烁晶体为由多个晶体构成的晶体阵列或整块连续晶体。
  4. 根据权利要求2所述的探测装置，其特征在于，所述光电转换器件包括单光子雪崩二极管、光电倍增管和硅光电倍增器中的一种或多种。
  5. 根据权利要求2所述的探测装置，其特征在于，所述耦合层由光学硅脂或光学玻璃组成。
  6. 根据权利要求1所述的探测装置，其特征在于，所述固定结构包括敷贴和/或固定胶，其中，所述敷贴包覆所述探测器的外表面，并且所述敷贴上设有用于输出所述探测器产生的电信号的开口；所述固定胶粘接在所述探测器的底部上。
  7. 根据权利要求1所述的探测装置，其特征在于，所述探测装置还包括：
    准直器，用于将所述放射性射线的入射方向进行准直，并使准直后的放射性射线进入所述探测器，所述准直器设置在所述探测器与所述固定结构之间并且通过所述固定结构而固定于所述目标区域所对应的表面。
  8. 根据权利要求7所述的探测装置，其特征在于，所述准直器包括一个或多个准直层，每个准直层上设有一个或多个通孔，并且当所述准直器包括多个准直层时，至少有两个准直层之间是错位耦合的。
  9. 根据权利要求7所述的探测装置，其特征在于，所述准直器的长度根据所述目标区域的位置来调节。
  10. 根据权利要求2所述的探测装置，其特征在于，所述探测装置还包括：
    第一包裹层，设置于所述闪烁晶体的周围。
  11. 根据权利要求10所述的探测装置，其特征在于，所述第一包裹层包括以下结构中的一种：由硫酸钡、锡纸以及遮光胶带组成的三层结构、由硫酸钡和锡纸组成的两层结构、由特氟龙组成的单层结构、由特氟龙和遮光胶带组成的两层结构、或者由特氟龙和锡纸组成的两层结构，其中，所述硫酸钡或所述特氟龙位于所述第一包裹层的最内层并且贴附于所述闪烁晶体的外表面，所述锡纸用于包裹所述硫酸钡或所述特氟龙，所述遮光胶带位于所述第一包裹层的最外层。
  12. 根据权利要求1所述的探测装置，其特征在于，所述探测装置还包括：
    传输结构，用于将所述探测器产生的电信号传输至所述处理器，并且其包括有线传输模块和/或无线传输模块。
  13. 一种成像系统，其特征在于，包括：权利要求1-12中任一项所述的探测装置以及图像重建装置，所述图像重建装置用于对所述探测装置中的所述探测器所产生的电信号进行图像重建以得到所述目标生物体内的所述目标区域的分布图像。
  14. 根据权利要求13所述的成像系统，其特征在于，所述成像系统还包括：
    辅助装置，其与所述探测装置一起配合使用，并且包括γ照相机、平板PET、平板SPECT、PET整机和SPECT整机中的一种或多种。
  15. 一种利用权利要求1-12任一项所述的探测装置对生物体进行探测的方法，其特征在于，所述方法包括：
    步骤S1：利用固定结构将探测器固定在目标生物体中的目标区域所对应的表面；
    步骤S2：利用所述探测器探测从所述目标生物体发出的放射性射线并产生对应的电信号；
    步骤S3：利用处理器对所述探测器所产生的电信号进行处理以确定出所述目标区域的放射性活度。
  16. 根据权利要求15所述的方法，其特征在于，在步骤S1之前，所述方法还包括：
    步骤S0，利用所述探测器和所述处理器确定所述目标生物体中的所述目标区域。
  17. 根据权利要求15或16所述的方法，其特征在于，在步骤S2之前，所述方法还包括：
    利用准直器对从所述目标生物体发出的所述放射性射线进行准直，并使准直后的所述放射性射线进入所述探测器。
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