CN109581460B - Composite detection device - Google Patents
Composite detection device Download PDFInfo
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- CN109581460B CN109581460B CN201811541860.0A CN201811541860A CN109581460B CN 109581460 B CN109581460 B CN 109581460B CN 201811541860 A CN201811541860 A CN 201811541860A CN 109581460 B CN109581460 B CN 109581460B
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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
- G01T1/1603—Measuring radiation intensity with a combination of at least two different types of detector
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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
- G01T1/20—Measuring radiation intensity with scintillation detectors
- G01T1/202—Measuring radiation intensity with scintillation detectors the detector being a crystal
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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
- G01T1/20—Measuring radiation intensity with scintillation detectors
- G01T1/203—Measuring radiation intensity with scintillation detectors the detector being made of plastics
Abstract
The embodiment of the application discloses compound detection device, it includes: the detection unit comprises a plastic scintillator, an inorganic scintillation crystal array and a photoelectric converter array which are sequentially arranged, wherein the plastic scintillator is used for receiving radioactive rays emitted from a target sample and generating a corresponding first visible light signal, the inorganic scintillation crystal array is used for receiving the radioactive rays emitted from the target sample and generating a corresponding second visible light signal, and the photoelectric converter array is used for respectively converting the first visible light signal and the second visible light signal into a first electric signal and a second electric signal; a signal processing unit for processing the first and second electrical signals to determine the type of radioactive rays; and an imaging unit for imaging the target sample according to a signal processing result of the signal processing unit. By utilizing the composite detection device provided by the embodiment of the application, the purpose of simultaneously detecting beta rays and high-energy gamma rays can be realized.
Description
Technical Field
The application relates to the field of radiation detection, in particular to a composite detection device.
Background
The statements in this section merely provide background information related to the present disclosure and may not constitute prior art.
The radiation detector can be widely applied to the fields of nuclear medicine, security inspection, astrophysics, autoradiography and the like. Currently, in the field of autoradiography, the existing radiation detectors mainly include the following types:
(1) radiation detectors using plastic scintillators and Charge Coupled Devices (CCDs), which use primarily beta-ray radioisotope nuclides (e.g.,14C、35S、32p, etc.) as radioactive tracers with spatial resolution up to tens of microns, but the dynamics of the radiation detectorThe detection range is small, the sensitivity is low, the gamma rays with the energy exceeding 30keV cannot be detected, the method is not suitable for detecting the gamma rays with high energy, and the cost is high.
(2) Radiation detectors using fluorescent phosphor screen technology, which primarily detect beta rays and gamma rays of lower energy (e.g. below 511keV), are also not suitable for detecting gamma rays of higher energy (e.g. above 511 keV).
Disclosure of Invention
It is an object of embodiments of the present application to provide a composite detection apparatus for the purpose of simultaneously detecting beta rays and gamma rays of high energy (i.e., energies above 511 keV).
In order to achieve the above object, an embodiment of the present application provides a composite detection apparatus, which includes:
the detection unit comprises a plastic scintillator, an inorganic scintillation crystal array and a photoelectric converter array, wherein the plastic scintillator, the inorganic scintillation crystal array and the photoelectric converter array are sequentially arranged, the plastic scintillator is used for receiving radioactive rays emitted from a target sample and generating a corresponding first visible light signal, the inorganic scintillation crystal array is used for receiving the radioactive rays emitted from the target sample and generating a corresponding second visible light signal, the photoelectric converter array is used for respectively converting the first visible light signal and the second visible light signal into a first electric signal and a second electric signal, the plastic scintillator and the inorganic scintillation crystal array are connected through a first structure, and the inorganic scintillation crystal array and the photoelectric converter array are connected through a second structure;
a signal processing unit for processing the first and second electrical signals generated by the photoelectric converter array to determine the type of the radioactive rays, including beta rays and gamma rays; and an imaging unit for imaging the target sample according to a signal processing result of the signal processing unit.
Preferably, the plastic scintillator has a thickness of 0.01mm to 5mm, and a length and a width of 5mm to 50 mm.
Preferably, when the thickness of the target sample is 20 μm to 100 μm, the interval between the opposite plastic scintillators located at both sides of the target sample is 1mm to 10 mm.
Preferably, the gap between two adjacent inorganic scintillation crystals in the inorganic scintillation crystal array is 0.05 mm-0.9 mm, and the thickness of each inorganic scintillation crystal is 0.01 mm-10 mm.
Preferably, at least one of two surfaces of the inorganic scintillation crystal array that are in contact with the plastic scintillator and the photoelectric converter array is polished.
Preferably, the array of photo-converters comprises silicon photomultipliers, photomultiplier tubes, charge-coupled devices and/or avalanche photodiodes.
Preferably, the first and second structures each comprise an adhesive structure or a combination of a receiving structure and an adhesive structure.
Preferably, the bonding structure is composed of optical glue, silicone glue, AB glue and/or UV glue, and the receiving structure includes an optical light guide, optical glass or optical fiber.
Preferably, the receiving structure is partially cut or fully cut, and the width of the cutting gap of the receiving structure is 0.1mm to 0.5 mm.
Preferably, the receiving structure is a single-layer structure or a multi-layer structure with less than 10 layers, and the total thickness of the receiving structure is 0.1mm to 10 mm.
Preferably, the detection unit further comprises: a signal multiplexing circuit for performing signal multiplexing processing on the first electrical signal and the second electrical signal generated by the photoelectric converter array and sending the processed first electrical signal and the processed second electrical signal to the signal processing unit.
Preferably, the signal processing unit includes:
the sampling subunit is used for sampling the first electric signal and the second electric signal according to a preset voltage threshold so as to record the falling edge attenuation time of the first electric signal and the second electric signal;
a determining subunit for determining the type of the radioactive ray according to the falling edge decay times of the first and second electrical signals.
Preferably, the signal processing unit includes:
the first subunit is configured to divide the first electrical signal into a first electrical signal a and a second electrical signal a, divide the second electrical signal into a first electrical signal B and a second electrical signal B, delay time of the first electrical signal a and the first electrical signal B, and attenuate amplitudes of the second electrical signal a and the second electrical signal B;
the second subunit is configured to compare the amplitude of the first electrical signal a with the amplitude of the second electrical signal a, record a first time point when the amplitude of the first electrical signal a is equal to the amplitude of the second electrical signal a, compare the amplitude of the first electrical signal B with the amplitude of the second electrical signal B, and record a second time point when the amplitude of the first electrical signal B is equal to the amplitude of the second electrical signal B;
a third subunit for determining a type of the radioactive ray from the first point in time and the second point in time.
As can be seen from the above technical solutions provided in the embodiments of the present application, a combination of a plastic scintillator and an inorganic scintillation crystal array is used to detect radioactive rays emitted from a target sample, which can achieve the purpose of simultaneously detecting beta rays and gamma rays with high energy (for example, up to 1000keV), thereby expanding the dynamic detection range, expanding the application range of a composite detection device, and further improving the spatial resolution of imaging. In addition, by using the signal processing unit to determine the type of detected radioactive rays, the resulting decay events in the target sample can be accurately determined, thereby allowing for better assistance in medical studies.
Drawings
In order to more clearly illustrate the embodiments of the present application or the technical solutions in the prior art, the drawings needed to be used in the description of the embodiments or the prior art will be briefly introduced below, it is obvious that the drawings in the following description are only some embodiments described in the present application, and for those skilled in the art, other drawings can be obtained according to the drawings without any creative effort.
Fig. 1 is a schematic structural diagram of a composite detection apparatus according to an embodiment of the present disclosure;
FIG. 2 is a schematic diagram of a frame of the detection unit;
FIG. 3 is a schematic structural view of a detection unit;
FIG. 4 is another schematic structural view of a detection unit;
FIG. 5 is a schematic diagram of an MVT sampling method for determining an object for which radioactive rays are detected;
FIG. 6 is a schematic diagram of an object for which radioactive rays are detected being determined using a CFD method;
FIG. 7 is an image obtained when the target sample is rat brain tissue;
fig. 8 is a schematic diagram of a frame of the transfer unit.
Detailed Description
The technical solutions in the embodiments of the present application will be clearly and completely described below with reference to the drawings in the embodiments of the present application, and it is obvious that the described embodiments are only used for explaining a part of the embodiments of the present application, but not all embodiments, and are not intended to limit the scope of the present application or the claims. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present application.
It will be understood that when an element is referred to as being "disposed on" another element, it can be directly on the other element or intervening elements may also be present. When an element is referred to as being "connected/coupled" to another element, it can be directly connected/coupled to the other element or intervening elements may also be present. The term "connected/coupled" as used herein may include electrical and/or mechanical physical connections/couplings. The term "comprises/comprising" as used herein refers to the presence of features, steps or elements, but does not preclude the presence or addition of one or more other features, steps or elements. As used herein, the term "and/or" includes any and all combinations of one or more of the associated listed items.
Unless defined otherwise, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this application belongs. The terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting of the application.
In addition, in the description of the present application, the terms "first", "second", and the like are used for descriptive purposes only and to distinguish similar objects, and there is no order of precedence between the two, and no indication or implication of relative importance is to be inferred. In addition, in the description of the present application, "a plurality" means two or more unless otherwise specified.
In the embodiments of the present application, the target sample may refer to a tissue section, a whole section of an organism, and/or a cell smear, etc. injected with a radioactive compound (i.e., a compound on which a radionuclide is labeled), but is not limited thereto. The radioactive rays may refer to neutron rays, X-rays, gamma rays, beta rays, alpha rays, and/or the like. The electrical signal may refer to an electrical pulse signal, a continuous electrical signal, or a discrete electrical signal, among others.
The composite detection device provided by the embodiment of the present application is described in detail below with reference to the accompanying drawings.
As shown in fig. 1 to 3, embodiments of the present application provide a composite detection apparatus, which may include:
a detection unit 110, which can be used for detecting radioactive rays emitted from a target sample and generating corresponding electrical signals, and includes a plastic scintillator 111, an inorganic scintillation crystal array 112, and a photoelectric converter array 113, which are sequentially arranged, wherein the plastic scintillator 111 and the inorganic scintillation crystal array 112 are connected by a first structure 114, and the inorganic scintillation crystal array 112 and the photoelectric converter array 113 are connected by a second structure 115;
a signal processing unit 120 for processing the electrical signal generated by the detection unit 110 and determining the type of the radioactive ray detected by the detection unit 110 according to the falling edge decay time of the electrical signal; and
an imaging unit 130 for performing imaging according to the signal processing result of the signal processing unit 120. Specifically, the method comprises the following steps:
the plastic scintillator 111 may be configured to receive radioactive radiation (e.g., beta radiation) emitted from a target sample, generate a corresponding first visible light signal, and transmit the first visible light signal to the photoelectric converter array 113 via the inorganic scintillator crystal array 112, and may also transmit other radioactive radiation emitted from the target sample to the inorganic scintillator crystal array 112. The plastic scintillator 111 may be composed of a plurality of scintillator cells, and it may be obtained by processing polystyrene or polyvinyl toluene, but is not limited thereto. The thickness of the plastic scintillator 111 may be 0.01mm to 5mm, and preferably, may be 0.25 mm. Accordingly, the length and width of the plastic scintillator 111 may be both 5mm to 50mm, and preferably, may be 16mm, 18mm, 25mm, or the like. Further, when the number of the plastic scintillators 111 is plural, the distance in the length or thickness direction between the two opposing plastic scintillators 111 located on both sides of the target sample may be determined according to the thickness of the target sample. For example, when the thickness of the target sample (e.g., a frozen section) is 20 μm to 100 μm, the distance d between two opposing plastic scintillators 111 may be 1mm to 10mm, preferably 5mm, which is advantageous for improving the spatial resolution of subsequent imaging.
The inorganic scintillator crystal array 112 can be configured to receive radioactive radiation (e.g., gamma rays) emitted from a target sample, generate a corresponding second visible light signal, and transmit the generated second visible light signal and the first visible light signal transmitted by the plastic scintillator 111 to the photoelectric converter array 113. The number of the inorganic scintillator crystal arrays 112 may be single or plural. Each inorganic scintillation crystal array 112 can be composed of a single inorganic scintillation crystal or can be composed of multiple inorganic scintillation crystals of the same size or different sizes. The inorganic scintillation crystals can be a continuous block of crystals or can be partially or fully cut strips of crystals. Moreover, in the inorganic scintillation crystal array 112, a gap between two adjacent inorganic scintillation crystals may be 0.05mm to 0.2mm, 0.05mm to 0.10mm, 0.05mm to 0.5mm, 0.5mm to 0.9mm, or 0.05 to 0.9mm, and preferably, may be 0.05mm, 0.1mm, 0.15mm, or 0.5mm, or the like; the thickness of each inorganic scintillation crystal can be 0.01mm to 10mm, and the total thickness of the inorganic scintillation crystal array 112 can be less than 400mm, and its length and width can be the same or different from that of the plastic scintillator 111. In addition, the inorganic scintillation crystals in the inorganic scintillation crystal array 112 may include one or more of Yttrium Silicate (YSO) crystals, yttrium lutetium silicate (LYSO) crystals, Lutetium Silicate (LSO) crystals, Bismuth Germanate (BGO) crystals, barium fluoride (BaF2) crystals, lanthanum bromide (LaBr3) crystals, Yttrium Aluminate (YAP) crystals, lutetium aluminate (LuAP) crystals, sodium iodide (NaI) crystals, cesium iodide (CsI) crystals, and the like, but is not limited thereto.
In addition, at least one of two surfaces of the inorganic scintillation crystal array 112 that are in contact with the plastic scintillator 111 and the photoelectric converter array 113 may be polished, which may increase the number of transmission of the first visible light signal and the second visible light signal, reduce light loss, and may improve subsequent imaging quality.
The photoelectric converter array 113 may be configured to convert a first visible light signal generated by the plastic scintillator 111 and a second visible light signal generated by the inorganic scintillation crystal array 112 into a first electrical signal and a second electrical signal, respectively, and send the generated first electrical signal and second electrical signal to the signal processing unit 120. The photoelectric converter array 113 may include one or more identical or different photoelectric converters, wherein each photoelectric converter may correspond to one or more inorganic scintillation crystals. In addition, the overall size of the photoelectric converter array 113 may be the same as or different from the size of the inorganic scintillator crystal array 112. The size of each photoelectric converter may be determined according to the size of the corresponding inorganic scintillation crystal or may be matched with the size of the inorganic scintillation crystal, for example, when the inorganic scintillation crystal array 112 includes 40 × 40 inorganic scintillation crystals, the total size thereof may be 16mm × 16mm × 3mm (length × width × thickness), and 5 × 5 inorganic scintillation crystals correspond to one photoelectric converter, in which case, the photoelectric converter array 113 may include 8 × 8 photoelectric converters, the total size thereof may be 16mm × 16mm × 1.5mm, and the size of a single photoelectric converter may be 2mm × 2mm × 1.5 mm. Further, the photoelectric converters included in the photoelectric converter array 113 may be one or more of a silicon photomultiplier (SiPM), a photomultiplier tube (APD) (e.g., a position sensitive photomultiplier tube (PSPMT)), a Charge Coupled Device (CCD), or an Avalanche Photodiode (APD) (e.g., a Position Sensitive Avalanche Photodiode (PSAPD)), but are not limited thereto.
In addition, the number of the photoelectric converter arrays 113 may correspond to the number of the plastic scintillators 111 and the inorganic scintillation crystal arrays 112, which may each be one or more. For example, fig. 4 shows two plastic scintillators 111, two inorganic scintillator crystal arrays 112, and two photoelectric converter arrays 113, which constitute a pair of flat plates in which a target sample is located between the two plastic scintillators 111.
The first structure 114 and the second structure 115 may each include an adhesive structure or a combination of a receiving structure and an adhesive structure, wherein the adhesive structure may be composed of optical glue, silicon gel, AB glue and/or UV glue, the receiving structure may be a solid light guide with a light transmittance of more than 90%, such as an optical light guide (e.g., acrylic sheet), optical glass or optical fiber, etc., or may be a light guide plate with a light transmittance of more than 90%, but is not limited thereto. The receiving structure is in contact with the plastic scintillator 111, the inorganic scintillator crystal array 112, and the photoelectric converter array 113 through an adhesive structure. Moreover, the receiving structure can be partially cut (for example, half cut) or fully cut, and the specific cutting mode can be determined according to actual needs. The cutting slit of the receiving structure may correspond to a plurality of (for example, 2 to 3) inorganic scintillation crystals at the outermost side of the inorganic scintillation crystal array 112, and may have a width of 0.1mm to 0.5mm, 0.1mm to 0.2mm, 0.2mm to 0.3mm, 0.1mm to 0.4mm, 0.2mm to 0.4mm, 0.3mm to 0.5mm, or 0.4mm to 0.5mm, preferably 0.2mm, 0.3mm, or 0.4 mm. In addition, the receiving structure may be a single-layer or multi-layer structure, for example, it may include 1 to 10 layers, and the thickness of each layer may be the same or different. The total thickness of the receiving structure can be designed according to practical needs, and for example, can be about 0.1mm to 10mm, and preferably can be 1.5mm to 2mm, but is not limited thereto. The cross-sectional shape of the receiving structure may be rectangular or trapezoidal, or may be other shapes. By receiving the plastic scintillator 111, the inorganic scintillator crystal array 112, and the photoelectric converter array 113 with the receiving structure, it is possible to effectively detect the first visible light signal emitted from the edge region of the plastic scintillator 111 and the second visible light signal emitted from the edge region of the inorganic scintillator crystal array 112, so that the accuracy of the detection result can be improved.
In another embodiment of the present application, the detection unit 110 may further include a signal multiplexing circuit 116, which may be configured to perform signal multiplexing processing on the first electrical signal and the second electrical signal generated by the photoelectric converter array 113 and send the processed first electrical signal and the processed second electrical signal to the signal processing unit 120. Specifically, the signal multiplexing circuit 116 may include at least one of the following circuits: the radio frequency coil multiplexing circuit comprises a resistance network multiplexing circuit, a capacitance network multiplexing circuit, a transmission line multiplexing circuit, a cross multiplexing circuit and a radio frequency coil multiplexing circuit. The resistance network multiplexing circuit mainly converts X × y (where X and y are both positive integers greater than or equal to 2) electrical signals output from the photoelectric converter array 113 into X + y electrical signals, and then converts the X + y electrical signals into 4 corner signals (X) by using Anger-Logic algorithm in the prior art and the like+、X-、Y+And Y-) And 1 way time signal. For example, in the case of an 8 × 8 SiPM array of photoelectric converters, 64 electrical signals can be reduced to 5 by using a resistor network multiplexing circuit and Anger-Logic algorithm, which can greatly reduce the amount of subsequent data calculation. As for the other multiplexing circuits, reference may be made to the related description in the prior art, which is not described herein in detail. By using signal multiplexing circuit 116, the amount of subsequent data computation can be reduced,and thus the data processing speed can be increased.
The signal processing unit 120 may process the first and second electrical signals generated by the photoelectric converter array 113 or the first and second electrical signals multiplexed by the signal multiplexing circuit 116 by using a multi-voltage threshold sampling method, a digital analog-to-digital conversion (ADC) sampling method, an analog constant ratio timing determination (CFD) method, and the like. For example, for utilizing the multiple voltage threshold sampling method, the signal processing unit 120 may include (not shown in the figure): a sampling subunit operable to sample the first and second electrical signals according to a preset voltage threshold (e.g., 4), record a time when amplitudes of the first and second electrical signals reach the preset voltage threshold and a falling edge decay time of the first and second electrical signals; a determination subunit operable to determine the type of radioactive rays detected by the detection unit 110 from the falling edge decay times of the recorded first and second electrical signals. For example, when the falling edge decay time of the first electrical signal is about 3ns to 5ns, it can be determined that the plastic scintillator 111 detects the β -ray; when the falling edge decay time of the second electrical signal is about 40ns, it can be determined that the inorganic scintillation crystal array 112 detected gamma rays, as shown in FIG. 5. The signal processing unit 120 may further include a calculating subunit operable to calculate energy information of the first electrical signal and the second electrical signal from the voltage amplitudes recorded by the sampling subunit, and calculate, from the obtained energy information, a position of the scintillator cell in the plastic scintillator 111 that detects the β -ray and a position of the inorganic scintillator crystal in the inorganic scintillator crystal array 112 that detects the γ -ray. For another example, for utilizing the CFD method, the signal processing unit 120 may include: the first subunit may be configured to divide the first electrical signal and the second electrical signal into two electrical signals, that is, divide the first electrical signal into a first electrical signal a and a second electrical signal a, and divide the second electrical signal into a first electrical signal B and a second electrical signal B, and may be configured to perform delay processing on the time of the first electrical signal a and the time of the first electrical signal B, and perform attenuation processing on the amplitudes of the second electrical signal a and the second electrical signal B (for a specific manner of the delay processing and the attenuation processing, reference may be made to the prior art, and a description thereof is omitted); the second subunit is configured to compare the amplitude of the first electrical signal a with the amplitude of the second electrical signal a, record a first time point when the amplitude of the first electrical signal a is equal to the amplitude of the second electrical signal a, compare the amplitude of the first electrical signal B with the amplitude of the second electrical signal B, and record a second time point when the amplitude of the first electrical signal B is equal to the amplitude of the second electrical signal B, where the first time point and the second time point may be referred to as zero-crossing time points; a third subunit operable to determine a type of the radioactive ray from the first point in time and the second point in time. Specifically, if the time of two paths of electric signals in the first electric signal reaching the first time point is 3-10 ns, it can be determined that the plastic scintillator 111 detects the beta ray; if the time of two paths of electric signals in the second electric signals reaching the second time point is 30-50 ns, it can be determined that the inorganic scintillation crystal array 112 detects the gamma ray, as shown in fig. 6, and thus it can be determined that the detection unit 110 detects the beta ray and the gamma ray. The principle of the sampling method described above can be referred to the prior art and will not be described in detail here.
By determining the type of radioactive rays detected by the detection unit 110, the decay events generated by the target sample can be determined, and thus the location of the radionuclide can be determined, which can accurately locate the radionuclide and thus assist in medical research on the target sample.
The imaging unit 130 may image the target sample according to the signal processing result of the signal processing unit 120. For example, in the case where the detection unit 110 includes only one pair of the plastic scintillator, the inorganic scintillator crystal array, and the photoelectric conversion device array, the imaging unit 130 may image the target sample directly according to the positional information of the plastic scintillator and the inorganic scintillator crystal array and the energy information of the electrical signal in the signal processing result; for the case where the detection unit 110 includes a plurality of pairs (e.g., two pairs) of plastic scintillators, an inorganic scintillation crystal array, and a photoelectric conversion device array (as shown in fig. 3), the imaging unit 130 may further perform coincidence event processing according to time information of the electrical signals in the signal processing result, identify each generated coincidence event, and then perform image reconstruction on the electrical signals by using an analytical-type algorithm (e.g., a Filtered Back Projection (FBP) algorithm) or by using an iterative-type algorithm (e.g., an Ordered Subset Expectation Maximization (OSEM) algorithm and a maximum a posteriori probability (MAP)) according to the obtained information of the coincidence events, but is not limited thereto. When the target sample is rat brain tissue, the resulting image of the target sample can be as shown in fig. 7. In addition, the spatial resolution of the composite detection device can be known from the resulting image. For example, the spatial resolution can reach 200 μm for the case of a SiPM array of the Sensl F30035 series and 18F-FDG as the radiotracer.
In addition, the signal processing unit 120 and the imaging unit 130 may be provided independently or may be integrated into one body, and for example, both may be provided integrally in a computer.
In another embodiment of the present application, the composite detection apparatus may further include a transmission unit 140, which may be integrated on a Field Programmable Gate Array (FPGA) chip, as shown in fig. 8. The transmission unit 140 may transmit the signal processing result of the signal processing unit 120 and/or the image obtained by the imaging unit 130 to an external device (e.g., an upper computer) through a Media Access Control (MAC) module according to a first-in-first-out (FIFO) mechanism. In addition, the transmission unit 140 may also reply with corresponding data, such as a voltage threshold, a supply voltage of the photodetector array 112, and the like, in response to a request of an external device. In addition, the transmission unit 140 may also store information it receives through the MAC module in a Flash memory (Flash).
As can be seen from the above description, the embodiments of the present application detect radioactive rays emitted from a target sample by using a combination including a plastic scintillator capable of detecting beta rays and an inorganic scintillator crystal array capable of detecting high-energy gamma rays, determine whether the detected radioactive rays are beta rays or gamma rays by using a signal processing unit, and image the target sample by using an imaging unit according to a signal processing result of the signal processing unit, so that an image of the target sample can be obtained, which can achieve the purpose of simultaneously detecting beta rays and high-energy gamma rays, thereby expanding the detection dynamic range thereof and also expanding the application range of the composite detection apparatus. In addition, the signal processing unit in the composite detection device adopts a multi-voltage threshold sampling method to perform sampling processing on the electric signals, so that the time for subsequent imaging (generally only 2-10 minutes is needed) can be reduced, the effect of real-time imaging can be achieved, and the spatial resolution of images can be improved.
Although the present application provides a composite detection apparatus as described in the above embodiments or figures, more or less components may be included in the composite detection apparatus provided in the present application based on conventional or non-inventive efforts.
The devices, units, modules, etc. set forth in the above embodiments may be implemented by chips and/or entities, or by products with certain functions. For convenience of description, the above devices are described as being divided into various components for separate description in terms of functions. Of course, the functionality of the various components may be implemented in the same or multiple chips and/or entities in practicing the present application.
The embodiments in the present specification are described in a progressive manner, and the same and similar parts among the embodiments are referred to each other, and each embodiment focuses on the differences from the other embodiments.
The embodiments described above are described in order to enable those skilled in the art to understand and use the present application. It will be readily apparent to those skilled in the art that various modifications to these embodiments may be made, and the generic principles described herein may be applied to other embodiments without the use of the inventive faculty. Therefore, the present application is not limited to the above embodiments, and those skilled in the art should make improvements and modifications within the scope of the present application based on the disclosure of the present application.
Claims (12)
1. A composite detection device, characterized in that it comprises:
the detection unit comprises a plastic scintillator, an inorganic scintillation crystal array and a photoelectric converter array, wherein the plastic scintillator, the inorganic scintillation crystal array and the photoelectric converter array are sequentially arranged, the plastic scintillator is used for receiving radioactive rays emitted from a target sample and generating a corresponding first visible light signal, the inorganic scintillation crystal array is used for receiving the radioactive rays emitted from the target sample and generating a corresponding second visible light signal, the photoelectric converter array is used for respectively converting the first visible light signal and the second visible light signal into a first electric signal and a second electric signal, the plastic scintillator and the inorganic scintillation crystal array are connected through a first structure, and the inorganic scintillation crystal array and the photoelectric converter array are connected through a second structure;
a signal processing unit for processing the first and second electrical signals generated by the array of photoelectric converters to determine a type of the radioactive rays, the type of radioactive rays including beta rays and gamma rays, the gamma rays having an energy higher than 511 keV; and
an imaging unit for imaging the target sample according to a signal processing result of the signal processing unit, comprising: performing coincidence event processing according to the time information in the signal processing result, and performing image reconstruction processing according to the obtained coincidence event information to obtain an image of the target sample,
when the thickness of the target sample is 20-100 micrometers, the distance between two opposite plastic scintillators positioned on two sides of the target sample is 1-10 mm.
2. The composite detection device of claim 1, wherein the plastic scintillator has a thickness of 0.01mm to 5mm, and a length and a width of 5mm to 50 mm.
3. The composite detection device of claim 1, wherein a gap between two adjacent inorganic scintillation crystals in the array of inorganic scintillation crystals is 0.05mm to 0.9mm, and a thickness of each of the inorganic scintillation crystals is 0.01mm to 10 mm.
4. The composite detection device of claim 1, wherein at least one of two surfaces of the inorganic scintillation crystal array that are in contact with the plastic scintillator and the photoelectric converter array are polished.
5. The composite detection apparatus of claim 1, wherein the array of photoconverters comprises silicon photomultipliers, photomultiplier tubes, charge coupled devices, and/or avalanche photodiodes.
6. The composite detection device of claim 1, wherein the first structure and the second structure each comprise an adhesive structure or a combination of a receiving structure and an adhesive structure.
7. The composite detection device of claim 6, wherein the adhesive structure is composed of optical glue, silicone, AB glue, and/or UV glue, and the receiving structure comprises an optical light guide, optical glass, or optical fiber.
8. The composite detection device of claim 7, wherein the receiving structure is partially or fully cut, and the width of the cutting gap of the receiving structure is 0.1mm to 0.5 mm.
9. The composite detection device according to any one of claims 6 to 8, wherein the receiving structure is a single-layer structure or a multi-layer structure having less than 10 layers, and the total thickness of the receiving structure is 0.1mm to 10 mm.
10. The composite detection device of claim 1, wherein the detection unit further comprises:
a signal multiplexing circuit for performing signal multiplexing processing on the first electrical signal and the second electrical signal generated by the photoelectric converter array and sending the processed first electrical signal and the processed second electrical signal to the signal processing unit.
11. The composite detection device of claim 1, wherein the signal processing unit comprises:
the sampling subunit is used for sampling the first electric signal and the second electric signal according to a preset voltage threshold so as to record the falling edge attenuation time of the first electric signal and the second electric signal;
a determining subunit for determining the type of the radioactive ray according to the falling edge decay times of the first and second electrical signals.
12. The composite detection device of claim 1, wherein the signal processing unit comprises:
the first subunit is configured to divide the first electrical signal into a first electrical signal a and a second electrical signal a, divide the second electrical signal into a first electrical signal B and a second electrical signal B, delay time of the first electrical signal a and the first electrical signal B, and attenuate amplitudes of the second electrical signal a and the second electrical signal B;
the second subunit is configured to compare the amplitude of the first electrical signal a with the amplitude of the second electrical signal a, record a first time point when the amplitude of the first electrical signal a is equal to the amplitude of the second electrical signal a, compare the amplitude of the first electrical signal B with the amplitude of the second electrical signal B, and record a second time point when the amplitude of the first electrical signal B is equal to the amplitude of the second electrical signal B;
a third subunit for determining a type of the radioactive ray from the first point in time and the second point in time.
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| CN111158039B (en) * | 2020-01-02 | 2022-01-04 | 苏州瑞派宁科技有限公司 | Signal sampling and reconstruction method and device |
| CN111142148B (en) * | 2020-01-10 | 2022-05-20 | 南昌大学 | SQL (structured query language) inversion method of position-sensitive scintillation detector |
| CN111610151B (en) * | 2020-05-19 | 2021-10-19 | 南昌大学 | Mobile vehicle-mounted electromagnetic wave multi-spectrometer system and imaging method |
| CN111948694A (en) * | 2020-07-23 | 2020-11-17 | 南昌大学 | Scintillation detector test platform and method based on high-speed oscilloscope |
| CN112711060B (en) * | 2020-12-18 | 2022-10-04 | 兰州大学 | Multilayer scintillator beta-gamma mixed field detector probe |
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