WO2020125123A1

WO2020125123A1 - Scintillation crystal assembly and radiation detection device and system comprising same

Info

Publication number: WO2020125123A1
Application number: PCT/CN2019/108855
Authority: WO
Inventors: 姜浩; 王侃
Original assignee: 苏州瑞派宁科技有限公司
Priority date: 2018-12-21
Filing date: 2019-09-29
Publication date: 2020-06-25
Also published as: CN109407139A; CN109407139B

Abstract

A scintillation crystal assembly (100) comprises a first scintillation crystal (110) and a second scintillation crystal (120). The second scintillation crystal (120) is disposed outside the first scintillation crystal (110) and encloses the first scintillation crystal (110), and is provided with an opening (130) through which a ray passes to be incident on the first scintillation crystal (110). A light output of the first scintillation crystal (110) is greater than a light output of the second scintillation crystal (120). The scintillation crystal assembly (100) and a radiation detection device (1000) and system comprising the scintillation crystal assembly (100) can generate a more flattened energy-response measurement curve, thereby reducing measurement deviation with respect to absorbed dose rates.

Description

Combined scintillation crystal and radiation detection device and system including the combined scintillation crystal

Technical field

The present application relates to the field of radiation detection, in particular to a combined scintillation crystal and a radiation detection device and system including the combined scintillation crystal.

Background technique

The description in this section only provides background information related to the disclosure of this application and does not constitute prior art.

The scintillation crystal detector may include a scintillation crystal and a photoelectric converter, which provides device support for nuclear physics research, radiation measurement, and nuclear medical imaging equipment research. For the measurement of X, γ and other rays, the scintillation crystal detector has a significant advantage over the GM tube and semiconductor detector in terms of sensitivity. However, since scintillation crystals have different detection effects for rays of different energies, for research objects injected with the same dose rate, the detection efficiency is different, and different numbers of scintillation pulses are output, which makes the energy measured by the scintillation crystal detector The response curve is not flat, so that the measurement result of the absorbed dose rate (that is, the energy absorbed by the unit mass of material in a unit time after being irradiated) deviates greatly.

At present, the prior art mainly solves the problem of uneven energy response curve through the following two solutions:

(1) Use a metal barrier layer composed of lead, copper and other radiation blocking materials to wrap the scintillation crystals, so that some low energy rays can be blocked during detection, reducing the detection efficiency of low energy rays, thereby making the energy response curve flat;

(2) The method of electronic compensation is used. This method mainly uses a multi-channel comparator or an analog-to-digital converter (ADC) at the back end to divide the measured ray energy into multiple energy segments, and then for each energy segment Perform weight calculation to make the overall energy response curve flat.

In the process of implementing this application, the inventor found that there are at least the following problems in the prior art:

(1) For the method using a metal barrier layer, on the one hand, the wrapped radiation blocking material will reduce the sensitivity of the scintillation crystal detector, resulting in reduced performance; on the other hand, the wrapped radiation blocking material will occupy a certain volume, which will increase The volume of the large scintillation crystal detector.

(2) For the electronic compensation method, since the energy response of the scintillation crystal changes drastically in the low energy section (below 130keV), the energy response of the scintillation crystal tends to be stable in the high energy section, and the energy response curve must be corrected It needs to divide more energy segments, which puts forward higher requirements for the design of the back-end circuit. For example, for the way of using multiple comparators, as the number of energy segments increases, the number of comparators used will increase exponentially, which will not only increase the circuit size and power consumption, but also make the occupied The resources of the end processor increase; for the way of using the ADC, its count rate is limited due to the low sampling rate of the ADC, which will affect the performance of the scintillation crystal detector, and the cost is higher.

Summary of the invention

An object of the embodiments of the present application is to provide a combined scintillation crystal and a radiation detection device and system including the combined scintillation crystal to solve at least one problem in the prior art.

In order to solve the above technical problems, the embodiments of the present application provide a combined scintillation crystal. The combined scintillation crystal may include a first scintillation crystal and a second scintillation crystal, and the second scintillation crystal is disposed on the first scintillation crystal. The first scintillation crystal is externally wrapped and the second scintillation crystal is provided with an opening through which rays are incident on the first scintillation crystal, wherein the light output of the first scintillation crystal is Greater than the light output of the second scintillation crystal.

Preferably, the second scintillation crystal includes a first docking surface coupled with an external photoelectric converter, a second docking surface opposite to the first docking surface, and a connection between the first docking surface and the second The ray receiving surface of the butting surface, the opening is located between the ray receiving surface in the second scintillation crystal and the corresponding ray receiving surface in the first scintillation crystal, and the opening direction of the opening is The incident directions of the rays are parallel.

Preferably, the depth of at least one opening among all the openings formed in the second scintillation crystal is at least the depth of the ray receiving surface where the opening in the second scintillation crystal is located and the first Half the distance between the corresponding ray receiving surfaces in the scintillation crystal.

Preferably, the depth of all the openings on each ray receiving surface of the second scintillation crystal is equal to the distance between the ray receiving surface where the opening is located and the corresponding ray receiving surface in the first scintillation crystal distance.

Preferably, the diameter and/or depth of the plurality of openings on the second scintillation crystal are different from each other.

Preferably, the opening directions are the same and the intervals between adjacent openings are the same.

Preferably, the interval between each of the openings is the same as the diameter of the openings.

Preferably, the diameter of the opening is

Wherein, N represents the number of the openings, which is a positive integer, and L2 is the length of the ray receiving surface of the second scintillation crystal.

Preferably, the shape of the opening includes at least one of a square, a circle, a diamond, a triangle, and a sector.

Preferably, the ratio v between the total area of the opening and the total area of the second scintillation crystal is determined by the following formula:

S(E)=S ₁ (E)*v+(S ₁₂ (E)+S ₂ (E))*(1-v));

Where S(·) represents the energy response of the combined scintillation crystal, and S ₁ (E) and S ₂ (E) respectively represent that the first scintillation crystal and the The sensitivity of the second scintillation crystal, S ₁₂ (E) represents the sensitivity of the first scintillation crystal when the opening is not opened on the second scintillation crystal, E represents the energy of the ray, and E ₀ is the preset energy Threshold, K is a constant between 15% and 30%.

Preferably, the material of the first scintillation crystal includes bismuth germanate, lead tungstate, chromium tungstate or gadolinium silicate, and the material of the second scintillation crystal includes sodium iodide, cesium iodide, yttrium silicate or silicon Lutetium.

Preferably, the shapes of the first scintillation crystal and the second scintillation crystal include a cube, a rectangular parallelepiped, a cylinder, a sphere, a prism, a circular truncated cone, or a sector.

An embodiment of the present application further provides a radiation detection device, which includes an interconnected photoelectric converter, a signal processing component, and the above-mentioned combined scintillation crystal, wherein the second scintillation crystal and the photoelectricity in the combined scintillation crystal Converter coupling.

Preferably, the signal processing component includes an amplifier circuit, a comparator, a counter, and a microcontroller that are provided in sequence, wherein the amplifier circuit is connected to an input terminal of the comparator and the photoelectric converter, and the micro The controller is also connected to the other input of the comparator.

An embodiment of the present application further provides a radiation detection system, which includes a housing, a display, and the above-mentioned radiation detection device, wherein the radiation detection device is connected to the display and is covered by the housing.

It can be seen from the above technical solutions provided by the embodiments of the present application that the embodiments of the present application wrap the first scintillation crystal by using the second scintillation crystal, and open an opening in the second scintillation crystal, and the light output of the second scintillation crystal The amount is less than the light output of the first scintillation crystal, which can make the first scintillation crystal not only detect the high-energy rays passing through the second scintillation crystal, but also the rays incident from the opening, and the second scintillation crystal can block Part of the low-energy rays, and only high-energy rays are detected, so that the measured energy response curve becomes flat, which can reduce the measurement deviation of the absorbed dose rate.

BRIEF DESCRIPTION

In order to more clearly explain the embodiments of the present application or the technical solutions in the prior art, the following will briefly introduce the drawings used in the description of the embodiments or the prior art. Obviously, the drawings in the following description are only These are some of the embodiments described in this application. For those of ordinary skill in the art, without paying any creative labor, other drawings can also be obtained based on these drawings.

1 is a schematic diagram of a three-dimensional structure of a combined scintillation crystal provided by an embodiment of the present application;

2 is a schematic diagram of a two-dimensional structure of another combined scintillation crystal provided by an embodiment of the present application;

3 is a schematic diagram of a two-dimensional structure of another combined scintillation crystal provided by an embodiment of the present application;

FIG. 4 is a comparison diagram of the measured energy response curves of the second scintillation crystal with and without openings;

5 is a schematic structural diagram of a radiation detection device provided by an embodiment of the present application;

6 is a schematic structural diagram of a radiation detection system provided by an embodiment of the present application.

detailed description

The technical solutions in the embodiments of the present application will be described clearly and completely in the following with reference to the drawings in the embodiments of the present application. Obviously, the described embodiments are only used to explain a part of the embodiments of the present application, not all The embodiments are not intended to limit the scope of the application or claims. Based on the embodiments in the present application, all other embodiments obtained by those of ordinary skill in the art without creative efforts shall fall within the protection scope of the present application.

It should be noted that, when an element is referred to as being “placed on” another element, it can be directly placed on another element or there can also be a centered element. When an element is referred to as being "connected/coupled" to another element, it may be directly connected/coupled to the other element or there may be both centered elements. The term "connection/coupling" as used herein may include electrical and/or mechanical physical connection/coupling. The term "comprising" as used herein 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. As used herein, the term "and/or" includes any and all combinations of one or more of the associated listed items.

Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by those skilled in the technical field of the present application. The terminology used herein is for the purpose of describing specific embodiments only, and is not intended to limit the present application.

In addition, in the description of this application, the terms "first", "second", etc. are used only for the purpose of describing and distinguishing similar objects, there is no order between the two, nor can it be understood as indicating or implying that they are relatively important Sex. In addition, in the description of the present application, unless otherwise stated, "plurality" means two or more.

The combined scintillation crystal and the radiation detection device and system including the combined scintillation crystal provided by the embodiments of the present application will be described in detail below with reference to the drawings.

As shown in FIGS. 1 and 2, an embodiment of the present application provides a combined scintillation crystal 100, which may include a first scintillation crystal 110 and a second scintillation crystal 120, where the second scintillation crystal 120 may be disposed on the first scintillation crystal The outer part of the crystal 110 wraps the first scintillation crystal 110, and the second scintillation crystal 120 may be provided with an opening 130 through which rays are incident on the first scintillation crystal 110. The rays may be from the source Or injected with a target sample injected with nuclide.

The first scintillation crystal 110 may be used to detect the rays incident through the opening 130 on the second scintillation crystal 120 and the high-energy rays remaining after being blocked by the second scintillation crystal 120, which may be a continuous scintillation crystal, or may It consists of multiple scintillation crystal strips or scintillation crystal blocks that are cut. The first scintillation crystal 110 may include multiple radiation receiving surfaces, and may be composed of materials such as bismuth germanate (BGO), lead tungstate (PbWO4), chromium tungstate (CdWO4), or gadolinium silicate (GSO), but not limited to this. The first scintillation crystal 110 may be in the shape of a cube, a rectangular parallelepiped, a cylinder, a sphere, a prism, a truncated cone, or a sector, but is not limited thereto. In addition, the light output of the first scintillation crystal 110 can be greater than the light output of the second scintillation crystal 120, so that in the subsequent processing, for the same amplitude threshold of the electrical signal, the low detection of the second scintillation crystal 120 can be filtered Energy rays, and only deal with the high-energy rays it detects.

The second scintillation crystal 120 may be used to detect high-energy rays and block a portion of low-energy rays from entering the first scintillation crystal 110. The second scintillation crystal 120 may be composed of materials such as sodium iodide (NaI), cesium iodide (CsI), yttrium silicate (YSO), or lutetium silicate (LSO), but is not limited thereto. Moreover, the second scintillation crystal 120 may be any shape capable of wrapping the first scintillation crystal 110, for example, a cube, a rectangular parallelepiped, a cylinder, a sphere, a prism, a circular truncated cone, or a fan-shaped body, etc., but it is not limited thereto, and its shape may be the same as that of the first scintillation crystal The crystals 110 are the same or different. The thickness or height of the second scintillation crystal 120 may be greater than the thickness or height of the first scintillation crystal 110, and the length thereof may be greater than or equal to the length of the first scintillation crystal 110. The specific size of the second scintillation crystal 120 may be determined according to the size and performance of the first scintillation crystal 110. It should be noted that the lengths of the first scintillation crystal 110 and the second scintillation crystal 120 may refer to the length of the side along which the opening is provided. In addition, when the first scintillation crystal 110 and the second scintillation crystal 120 are in the shape of a sphere, a cylinder, or a truncated cone, the length can indicate the diameter.

The second scintillation crystal 120 may include a first docking surface coupled with an external photoelectric converter, a second docking surface opposite to the first docking surface, and one or more ray receivers connecting the first docking surface and the second docking surface Surface (ie, the surface receiving the radiation), the opening 130 may be located between at least one of the plurality of (eg, 4) radiation receiving surfaces and the corresponding radiation receiving surface on the first scintillation crystal 110, and The opening direction of the opening 130 is parallel to the incident direction of the rays, so as to increase the amount of light detected. It should be noted that although only two opposing radiation receiving surfaces of the second scintillation crystal 120 are provided with openings in the drawings, the other two opposing radiation receiving surfaces may also be provided with openings .

In addition, the second scintillation crystal 120 may be provided with a plurality of openings 130, and at least one of the openings 130 may have a depth of at least the ray receiving surface where the opening 130 in the second scintillation crystal 120 is located. Half the distance from the corresponding ray receiving surface in the first scintillation crystal 110. Preferably, the depth of all the openings 130 may be equal to the distance between the ray receiving surface where the opening 130 in the second scintillation crystal 120 is located and the corresponding ray receiving surface in the first scintillation crystal 110, as shown in FIG. 1 For example, the depths of the five openings 130 in the ray receiving surface A1 of the second scintillation crystal 120 are all equal to the distance between the ray receiving surface A1 and the ray receiving surface A1′ of the first scintillation crystal, so as to pass through the opening 130 The incident rays are directly incident on the first scintillation crystal 110, so that the first scintillation crystal 110 can detect the rays of the full energy segment (including the low energy segment and the high energy segment). Moreover, the depth and/or diameter of each opening 130 may be the same or different, as shown in FIG. 3.

In addition, the axis of the opening 130 on the opposite ray receiving surface in the second scintillation crystal 120 may be located on a straight line, which may be parallel to the width or height of the second scintillation crystal 120. Each opening 130 may be polygonal (for example, square, triangular, diamond, etc.), circular, or fan-shaped, but is not limited thereto. The size and shape of each opening 130 may be the same or different, and it may be the same as or different from the shapes of the first scintillation crystal 110 and the second scintillation crystal 120. Moreover, the intervals d between the adjacent openings 130 in the same opening direction may also be the same or different. In addition, the interval between adjacent openings 130 may be the same as or different from the diameter of the openings 130. The diameter of each opening 130 can be

In which, N represents the number of openings 130, which is a positive integer, L2 is the length of the ray receiving surface of the second scintillation crystal 120, preferably, the diameter of each opening 130 may be

or

Wait. It should be noted that when the opening has a polygonal shape such as a square, triangle, or rhombus, the diameter may also represent the length of the side parallel to the radiation receiving surface of the second scintillation crystal 120.

In addition, in the case of determining the size of the second scintillation crystal 120, the area ratio of the predetermined opening 130 to the second scintillation crystal 120 may be determined (ie, the total area of the opening 130 and the total area of the second scintillation crystal 120 Ratio) to determine the size of each opening. For each opening 130 having the same size, the total area of all the openings 130 can be divided by the number of openings 130 to determine the size of each opening 130; for multiple openings 130 The size of the different openings may be different. You can determine the openings of each opening 130 based on the preset lower threshold (for example, 1/6) of the area of each opening 130 taking up the total area of all openings 130. area. The area ratio v of the opening 130 to the second scintillation crystal 120 can be determined by the following formula:

S(E)=S ₁ (E)*v+(S ₁₂ (E)+S ₂ (E))*(1-v)) (1)

Among them, S(·) represents the energy response of the combined scintillation crystal; S ₁ (E) and S ₂ (E) respectively represent the first scintillation crystal 110 and the second scintillation crystal 120 when the second scintillation crystal 120 is provided with an opening 130 Sensitivity, S ₁₂ (E) represents the sensitivity of the first scintillation crystal 110 when no opening 130 is formed on the second scintillation crystal 120, all three can be measured in advance, and its unit is CPS/μGy/h; E Represents the energy of the ray; E ₀ is the preset energy threshold. For different sources, it can take different values. For example, for a ¹³⁷ Cs source, E ₀ can be 662 keV; K is between 15% and 30% The constant is preferably 20% or 30%.

It can be seen from the above description that the embodiment of the present application wraps the first scintillation crystal by using the second scintillation crystal, and opens an opening in the second scintillation crystal, which can make the first scintillation crystal not only detect The high-energy rays of the second scintillation crystal can also detect the rays incident from the opening, and the second scintillation crystal can block some low-energy rays, which can reduce the sensitivity to low-energy rays, and only detect high-energy rays, which can Increase the sensitivity to high-energy rays, so that the subsequent energy response curve becomes flat, as shown in Figure 4. In FIG. 4, the black curve represents the energy response curve measured when the second scintillation crystal is not perforated, and the gray curve represents the energy response curve measured when the second scintillation crystal is perforated. According to FIG. 4, compared with the case where the second scintillation crystal is not opened, by using the combined scintillation crystal provided by the present application, the measured energy response curve can be made flatter, which can reduce the measurement of the absorbed dose rate deviation. In addition, in the embodiments of the present application, the second scintillation crystal is used to replace the traditional metal barrier layer, which can avoid the decrease in sensitivity and reduce the volume.

An embodiment of the present application further provides a radiation detection device 1000, as shown in FIG. 5, which may include the above-mentioned combined scintillation crystal 100, photoelectric converter 200, and signal processing component 300.

Among them, the photoelectric converter 200 is coupled with the combined scintillation crystal 100, and can be used to convert the combined scintillation crystal 100 to an optical signal generated in response to the detected rays into an electrical signal. The photoelectric converter 200 may be a silicon photomultiplier (SiPM), photomultiplier tube (PMT), avalanche photodiode (APD), or the like, and its size may be determined according to the size of the combined scintillation crystal 100.

The signal processing component 300 can be used to digitize the electrical signal generated by the photoelectric converter 200. The signal processing component 300 may include an amplifier circuit 310, a comparator 320, a counter 330, and a microcontroller 340 connected to each other. The amplifier circuit 310 can be used to amplify and shape the electrical signal generated by the photoelectric converter 200; an input terminal (for example, a positive input terminal) of the comparator 320 can be connected to the output terminal of the amplifier circuit 310, and can be used to The amplitude (for example, voltage) of the electrical signal amplified by the amplification circuit 310 is compared with a preset amplitude threshold and a comparison result is output. Specifically, when the amplitude of the electrical signal is greater than or equal to the preset amplitude threshold, it can output 1, When the amplitude of the electrical signal is less than the preset amplitude threshold, it can output 0, and when the output of the comparator 320 goes from 1 to 0 or from 0 to 1, it can generate a state transition; the counter 330 can be used to compare the comparator 320 counts the number of state transitions; the microcontroller 340 can be connected to the other input (eg, negative input) of the comparator 320 to set the reference voltage of the comparator 320 (ie, a preset amplitude threshold) And, the microcontroller can be used to calculate the energy response of the combined scintillation crystal according to the counting result of the counter (ie, the sensitivity change of the combined scintillation crystal for rays of different energies).

It can be seen from the above description that in the embodiments of the present application, only one comparator is required, and no multiple comparator or ADC circuit is required, which can reduce the complexity and power consumption of the radiation detection device, and can also reduce costs.

An embodiment of the present application further provides a radiation detection system. As shown in FIG. 6, it may include the above-mentioned radiation detection device 1000, and may further include a housing 1100 and a display 1200. The display 1200 can be connected to the radiation detection device 1000 to display the processing result; the housing 1100 can be used to wrap the radiation detection device 1000 in it, so as to prevent it from being damaged by the outside world.

Although the present application provides the combined scintillation crystal and the radiation detection device and system including the combined scintillation crystal as described in the above embodiments or drawings, the radiation detection device and system provided in the present application are based on conventional or without creative labor More or fewer components can be included.

The systems, devices, components, modules, etc. explained in the above embodiments may be specifically implemented by chips and/or entities, or implemented by products with certain functions. For the convenience of description, when describing the above device, the functions are divided into various components and described separately. Of course, when implementing this application, the functions of each component may be implemented in one or more chips and/or entities.

The embodiments in this specification are described in a progressive manner. The same or similar parts between the embodiments can be referred to each other. Each embodiment focuses on the differences from other embodiments.

The above-mentioned embodiments are described to facilitate those skilled in the art to understand and use this application. Those skilled in the art can obviously make various modifications to these embodiments, and apply the general principles described here to other embodiments without creative work. Therefore, the present application is not limited to the above-mentioned embodiments. According to the disclosure of the present application, those skilled in the art should make improvements and modifications without departing from the scope of the present application within the protection scope of the present application.

Claims

A combined scintillation crystal, characterized in that the combined scintillation crystal includes a first scintillation crystal and a second scintillation crystal, and the second scintillation crystal is disposed outside the first scintillation crystal and wraps the first scintillation crystal , And the second scintillation crystal is provided with an opening through which rays are incident on the first scintillation crystal, wherein the light output of the first scintillation crystal is greater than the light of the second scintillation crystal Output volume.
The combined scintillation crystal according to claim 1, wherein the second scintillation crystal includes a first butt surface coupled to an external photoelectric converter, a second butt surface opposed to the first butted surface, and A ray receiving surface connecting the first butting surface and the second butting surface, the opening is located between the ray receiving surface in the second scintillation crystal and the corresponding ray receiving surface in the first scintillation crystal , And the opening direction of the opening is parallel to the incident direction of the rays.
The combined scintillation crystal according to claim 2, wherein at least one of all the openings formed on the second scintillation crystal has a depth at least equal to that of the second scintillation crystal Half the distance between the radiation receiving surface where the opening is located and the corresponding radiation receiving surface in the first scintillation crystal.
The combined scintillation crystal of claim 3, wherein the depth of all the openings on each ray receiving surface of the second scintillation crystal is equal to the ray receiving surface where the opening is located and the first The distance between corresponding ray receiving surfaces in a scintillation crystal.
The combined scintillation crystal according to claim 2 or 3, wherein the diameter and/or depth of the plurality of openings on the second scintillation crystal are different from each other.
The combined scintillation crystal according to claim 1, wherein the opening directions are the same and the intervals between adjacent openings are the same.
The combined scintillation crystal according to claim 6, wherein the spacing between each of the openings is the same as the diameter of the openings.
The combined scintillation crystal according to claim 2 or 7, wherein the diameter of the opening is
Wherein, N represents the number of the openings, which is a positive integer, and L 2 is the length of the ray receiving surface of the second scintillation crystal.
The combined scintillation crystal according to claim 1, wherein the shape of the opening includes at least one of a square, a circle, a diamond, a triangle, and a sector.
The combined scintillation crystal according to claim 1, wherein the ratio v between the total area of the opening and the total area of the second scintillation crystal is determined by the following formula:

S(E)=S 1 (E)*v+(S 12 (E)+S 2 (E))*(1-v));

Where S(·) represents the energy response of the combined scintillation crystal, and S 1 (E) and S 2 (E) respectively represent that the first scintillation crystal and the The sensitivity of the second scintillation crystal, S 12 (E) represents the sensitivity of the first scintillation crystal when the opening is not opened on the second scintillation crystal, E represents the energy of the ray, and E 0 is the preset energy Threshold, K is a constant between 15% and 30%.
The combined scintillation crystal of claim 1, wherein the material of the first scintillation crystal includes bismuth germanate, lead tungstate, chromium tungstate, or gadolinium silicate, and the material of the second scintillation crystal includes iodine Sodium hydroxide, cesium iodide, yttrium silicate or lutetium silicate.
The combined scintillation crystal according to claim 1, wherein the shapes of the first scintillation crystal and the second scintillation crystal include a cube, a rectangular parallelepiped, a cylinder, a sphere, a prism, a circular truncated cone, or a sector.
A radiation detection device comprising a photoelectric converter and a signal processing assembly connected to each other, characterized in that the radiation detection device further comprises the combined scintillation crystal according to any one of claims 1 to 12, wherein the combination The second scintillation crystal in the scintillation crystal is coupled with the photoelectric converter.
The radiation detection device according to claim 13, wherein the signal processing component includes an amplifier circuit, a comparator, a counter, and a microcontroller that are sequentially arranged, wherein the amplifier circuit and one input of the comparator Is connected to the photoelectric converter, and the microcontroller is also connected to the other input of the comparator.
A radiation detection system, including a housing and a display, characterized in that the radiation detection system further includes the radiation detection device of claim 13 or 14, wherein the radiation detection device is connected to the display and is The shell is wrapped inside.