A CT detection device and temperature control method thereof

Abstract

The present invention provides a CT detection device and a temperature control method thereof, the detection device comprises a base, a control module arranged on the base and a plurality of detection modules, each detection module comprises: a metal bracket, the metal bracket is fixed to the base; a scintillator and a conversion unit connected to the scintillator, the scintillator and the conversion unit are arranged on the same surface of the metal bracket relative to each other, the scintillator is exposed outside the base and is used to receive X-rays, and the conversion unit is used to process the X-rays; a closed-loop heating unit, the closed-loop heating unit is arranged on the surface of the metal bracket away from the scintillator, is electrically connected to the control module, and is used to adjust the current temperature of the scintillator to maintain it at the preset working temperature when the self-heat of the conversion unit cannot maintain the scintillator at the preset working temperature. The detection device provided by the present invention can maintain the preset working temperature of the scintillator and improve the quality of the scanned image.

Description

Technical Field

[0001] The present invention relates to the field of medical imaging technology, and in particular to a CT detection device and a temperature control method thereof. Background Art

[0002] X-ray CT is the abbreviation of X-ray tomography technology. The tomographic image of the scanned object is obtained by reconstructing CT data. The dangerous items in the scanned object are identified by analyzing the characteristic data in the tomographic image.

[0003] The core component of a CT machine is the detector, which is mainly composed of gratings, scintillators, photoelectric sensor units, AD converters and other components. Some important characteristics of these components are sensitive to temperature. Among them, the scintillator needs to work at a relatively stable temperature and is very sensitive to temperature changes. At this time, the scintillator and its surrounding environment need to be temperature controlled. Uneven temperature distribution of different scintillators in the CT detector will lead to inconsistent responses of different detector modules, resulting in abnormal CT detectors and affecting image quality.

[0004] At present, the temperature control strategy for detectors is to control the temperature of the detector by adjusting the temperature of the air around the detector. However, when the external environment temperature is stable, this adjustment method is limited to controlling the temperature within a temperature difference of ±2°C, and the material temperature characteristics of the scintillator are relatively high. Once the external environment temperature changes significantly, it takes a long time to adjust the detector temperature to the operating temperature and reach a steady state. Summary of the invention

[0005] The object of the present invention is to provide a CT detection device and a temperature control method thereof, which can solve at least one of the above-mentioned technical problems. The specific scheme is as follows:

[0006] According to a specific embodiment of the present invention, in a first aspect, the present invention provides a CT detection device, comprising a base, a control module disposed on the base, and a plurality of detection modules, each detection module comprising:

[0007] A metal bracket, the metal bracket is fixed to the base;

[0008] a scintillator and a conversion unit connected to the scintillator, wherein the scintillator and the conversion unit are arranged on the same surface of the metal bracket opposite to each other, the scintillator is exposed outside the base and is used to receive X-rays, and the conversion unit is used to process the X-rays;

[0009] A closed-loop heating unit is arranged on the surface of the metal bracket away from the scintillator and is electrically connected to the control module. When the spontaneous heat of the conversion unit cannot maintain the scintillator at the preset operating temperature, the closed-loop heating unit is used to adjust the current temperature of the scintillator to maintain it at the preset operating temperature.

[0010] Optionally, the closed-loop heating unit includes a heating resistor and a temperature sensor, and the heating resistor and the temperature sensor are both arranged on the surface of the metal bracket facing away from the scintillator, and are electrically connected to the control module respectively; wherein the temperature sensor is used to collect the real-time temperature of the surface of the metal bracket; the control module controls the heating resistor to generate heat according to the real-time temperature of the surface of the metal bracket, and the heat is transmitted to the scintillator through the metal bracket.

[0011] Optionally, the heating resistor is a thin film thermal resistor, and the thin film thermal resistor is adhered to the surface of the metal bracket.

[0012] Optionally, the control module includes a pulse width modulation circuit, which is used to control the power of the heating resistor to generate different amounts of heat.

[0013] Optionally, the control module further includes a processing unit, which is used to receive the real-time temperature of the metal bracket surface collected by the temperature sensor, and obtain the current temperature of the scintillator according to the real-time temperature of the metal bracket surface.

[0014] Optionally, the temperature of the scintillator changes linearly with the change of the real-time temperature of the surface of the metal support.

[0015] Optionally, the metal bracket is a sheet-like structure, which is used to transfer the self-heat of the conversion unit and the heat generated by the closed-loop heating unit to the scintillator.

[0016] Optionally, when the scintillator is in equilibrium, the real-time temperature difference is within ±0.5°C.

[0017] According to a specific embodiment of the present invention, in a second aspect, the present invention provides a temperature control method for a CT detection device as described above, comprising: when the spontaneous heat generated by the conversion unit makes the scintillator reach a preset operating temperature, the surface temperature of the metal bracket is collected in real time; if the surface temperature of the metal bracket is lower than the preset operating temperature, the closed-loop heating unit is controlled to work, and the generated heat is transferred to the scintillator through the metal bracket; when the real-time temperature of the scintillator reaches the preset operating temperature, the closed-loop heating unit is controlled to stop working, and the conversion unit transfers the spontaneous heat to the scintillator to maintain it at the preset operating temperature.

[0018] Optionally, the method further includes: in the process of the conversion unit generating self-heat, controlling the closed-loop heating unit to operate and transferring the generated heat to the conversion unit until the self-heat of the conversion unit reaches a preset operating temperature of the scintillator, at which time the closed-loop heating unit stops operating.

[0019] Compared with the prior art, the above solution of the embodiment of the present invention has at least the following beneficial effects:

[0020] First, the present invention can improve the quality of scanned images by controlling the scintillator temperature in a distributed manner so as to maintain it at a preset operating temperature;

[0021] Second, the real-time temperature difference of the detection device is controlled within ±0.5°C when it is in a steady state, which greatly reduces the requirements for the temperature characteristics of the scintillator. The purity and processing technology of the mainstream scintillator materials can be greatly relaxed, which reduces the cost of the scintillator while ensuring image quality.

[0022] Third, the CT detection device fully utilizes the self-heating energy of the conversion unit and reduces energy loss. BRIEF DESCRIPTION OF THE DRAWINGS

[0023] The drawings herein are incorporated into and constitute a part of the specification, showing embodiments consistent with the present invention, and together with the specification, are used to explain the principles of the present invention. Obviously, the drawings described below are only some embodiments of the present invention, and for those of ordinary skill in the art, other drawings can be obtained based on these drawings without creative work. In the drawings:

[0024] Figure 1 A schematic structural diagram of a CT detection device provided by an embodiment of the present invention is shown;

[0025] Figure 2 Shows Figure 1 A front view of the CT detection device shown;

[0026] Figure 3 Shows Figure 1 A top view of the CT detection device shown;

[0027] Figure 4 Shows Figure 1 A schematic diagram of the working principle of a closed-loop heating unit in a CT detection device is shown;

[0028] Figure 5 A flow chart of a temperature control method for a CT detection device provided by another embodiment of the present invention is shown. DETAILED DESCRIPTION

[0029] In order to make the purpose, technical scheme and advantages of the present invention clearer, the present invention will be further described in detail below with reference to the accompanying drawings. Obviously, the described embodiments are only part of the embodiments of the present invention, rather than all the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present invention.

[0030] The terms used in the embodiments of the present invention are only for the purpose of describing specific embodiments, and are not intended to limit the present invention. The singular forms "a", "said" and "the" used in the embodiments of the present invention and the appended claims are also intended to include plural forms, unless the context clearly indicates other meanings, and "multiple" generally includes at least two.

[0031] It should be understood that the term "and / or" used in this article is only a description of the association relationship of associated objects, indicating that there can be three relationships. For example, A and / or B can represent: A exists alone, A and B exist at the same time, and B exists alone. In addition, the character " / " in this article generally indicates that the associated objects before and after are in an "or" relationship.

[0032] It should be understood that although the terms first, second, third, etc. may be used to describe the embodiments of the present invention, they should not be limited to these terms.

[0033] It should also be noted that the term "includes", "comprising" or any other variation thereof is intended to cover non-exclusive inclusion, so that a commodity or device including a series of elements includes not only those elements, but also other elements not explicitly listed, or also includes elements inherent to such commodity or device. In the absence of more restrictions, the elements defined by the sentence "comprising a ..." do not exclude the existence of other identical elements in the commodity or device including the elements.

[0034] The optional embodiments of the present invention are described in detail below with reference to the accompanying drawings.

[0035] Example 1

[0036] Figure 1 A schematic diagram of the structure of a CT detection device is shown. Figure 2 Shows Figure 1 A front view of the CT detection device shown; Figure 3 Shows Figure 1 The top view of the CT detection device is shown in FIG. Figure 1-3 As shown, the CT detection device is arranged on the rotating frame of the CT machine, and is used to receive the X-rays emitted by the tube, and obtain a scanned image by performing signal processing on the X-rays. For the specific scanning principle, please refer to the records of the prior art about the CT machine.

[0037] like Figure 1-3 As shown, an embodiment of the present invention provides a CT detection device 100, including a base 10, a control module 20 disposed on the base, and a plurality of detection modules 30, each detection module 30 including:

[0038] A metal bracket 31, wherein the metal bracket 31 is fixed to the base 10;

[0039] a scintillator 32 and a conversion unit 33 connected to the scintillator, wherein the scintillator 32 and the conversion unit 33 are arranged on the same surface of the metal bracket 31 opposite to each other, the scintillator 32 is exposed outside the base 10 and is used to receive X-rays, and the conversion unit 33 is used to process the X-rays;

[0040] The closed-loop heating unit 34 is arranged on the surface of the metal bracket 31 away from the scintillator 32 and is electrically connected to the control module 20. When the spontaneous heat of the conversion unit 33 cannot maintain the scintillator at the preset operating temperature, the current temperature of the scintillator is adjusted to maintain it at the preset operating temperature.

[0041] The base 10 is mainly used for installation, and the detection device is fixed on the rotating frame (not shown) of the CT machine. The shape of the base 10 is not limited, and is set according to actual needs, as long as it can carry the control module 20 and multiple detection modules 30, and expose the scintillator part outside the base, for example, it can be an irregular shape, a rectangle, a trapezoid, etc.

[0042] In this embodiment, the base 10 includes a base 11, a first side wall 12 and a second side wall 13 disposed at two ends of the base, and an opening between the first side wall 12 and the second side wall 13. Each structure can be integrally injection molded or fixedly connected. The opening, the first side wall, the second side wall and the base form an internal space.

[0043] The multiple detection modules 30 are arranged at the opening of the base 10 and are sequentially extended along the first side wall 12 to the second side wall 13. The multiple detection modules 30 are independent of each other and do not interfere with each other. The temperature of each detection module 30 is controlled separately, and each detection module is regarded as an independent control area.

[0044] The metal bracket 31 is arranged at the opening and fixed to the base 10 through a heat insulation element, and is used to transfer all the self-heat of the conversion unit 33 and the heat generated by the closed-loop heating unit 34 to the scintillator 32 to avoid partial heat being transferred to the base 10, wherein the heat insulation element can be a plastic staple, heat insulation glue, etc.

[0045] The metal bracket 31 is a thin sheet structure made of metal material, which has a fast heat conduction speed and can improve the heat transfer efficiency. The metal material can be stainless steel, gold, silver and other materials. In this embodiment, the metal bracket 31 is a sheet-like rectangular structure, the length direction of the metal bracket is perpendicular to the extension direction of the multiple detection modules, and the width direction of the metal bracket is parallel to the extension direction of the multiple detection modules.

[0046] like Figure 3 As shown, the scintillator 32 is arranged on the side of the metal bracket 31 facing away from the internal space, and the conversion unit 33 is also arranged on the side facing away from the internal space, opposite to the scintillator and connected to the scintillator. Figure 3 The conversion unit is blocked by other structures such as a base and a shell. The scintillator 32 has an energy receiving surface facing the emission source, and the energy receiving surface is away from the surface of the metal bracket 31, and is used to receive the rays emitted by the emission source such as a tube. When high-energy particles in the rays hit the scintillator, the scintillator can convert the kinetic energy of the high-energy particles into light energy and emit flashes. The scintillator can exist in the form of crystals, so it can also be called a scintillating crystal. The scintillator is used to convert X-rays into visible light. In this embodiment, the scintillator 32 is attached to the surface of the metal bracket to facilitate rapid absorption of heat.

[0047] The conversion unit 33 includes a photoelectric converter 331 and an analog-to-digital conversion chip 332, forming a module circuit. The analog-to-digital conversion chip is connected to the side of the photoelectric converter away from the scintillator 32, and the photoelectric converter is arranged opposite to the scintillator. The photoelectric converter 331 is used to convert the optical signal into an electrical signal, and the analog-to-digital conversion chip 332 is used to convert the electrical signal of the photoelectric conversion device into a digital signal for processing by a back-end signal processing unit (not shown in the figure).

[0048] The conversion unit 33 will continuously generate self-heat during operation, rising from the current room temperature to the preset operating temperature of the scintillator, and then enter a self-heating maintenance state, which means that the temperature of the scintillator is controlled by the self-heat of the conversion unit. Since the self-heat of the conversion unit is slightly lower than the heat dissipation of the preset operating temperature equilibrium state, the temperature stability of the scintillator area can be ensured by adjusting the working state of the closed-loop heating unit. Among them, the preset operating temperature can be set according to the optimal operating temperature range of the CT detector. Generally, the optimal operating temperature of the scintillator is known.

[0049] The closed-loop heating unit 34 is used to perform temperature compensation based on the self-heat when the self-heat of the conversion unit 33 cannot maintain the scintillator at the preset operating temperature. That is to say, the self-heating energy of the conversion unit and the heat of the closed-loop heating unit are used together to control the scintillator temperature to be maintained at the preset operating temperature. In this process, the self-heating energy of the module circuit is fully utilized to reduce energy loss.

[0050] Specifically, Figure 1-4 As shown, the closed-loop heating unit 34 includes a heating resistor 341 and a temperature sensor 342, both of which are arranged on the surface of the metal bracket 31 away from the scintillator, and are electrically connected to the control module respectively; wherein the temperature sensor 342 is used to collect the real-time temperature of the metal bracket surface; the control module 20 controls the heating resistor 341 to generate heat according to the real-time temperature of the metal bracket surface, and the heat is transmitted to the scintillator 32 through the metal bracket 31. The heat dissipation efficiency of the metal bracket 31 surface is less than the heat conduction efficiency of the heating resistor 341 to the metal bracket 31, because the heat dissipation is mainly through the heat convection effect, and the heat absorption is through the heat conduction effect. According to the material properties, the heat convection efficiency is significantly lower than the heat conduction efficiency. In this embodiment, the heating resistor 341 and the scintillator 32 are arranged relative to each other on different surfaces.

[0051] It can be understood that the heating resistor 341 and the temperature sensor 342 are arranged on the same surface and both face the internal space to prevent damage. The heating resistor 341 is made of a material with good thermal conductivity, and different heat is generated by controlling its output power. The number of the heating resistors is not limited and can be one or more according to actual needs.

[0052] In this embodiment, the heating resistor 341 is a thin film thermal resistor, which is adhered to the surface of the metal bracket close to the internal space by heat-proof adhesive. The thin film thermal resistor can reduce the weight of the detection device, and the detection device has a simple structure and is easy to manufacture.

[0053] The sensitivity of the temperature sensor is less than 0.2°C. In this embodiment, the sensitivity of the temperature sensor used is 0.02°C ± 0.01°C. It should be noted that the temperature sensor 342 always collects the surface temperature of the metal bracket. Since the heat of the heating resistor is directly acted on the scintillator through the metal bracket, the temperature of the scintillator changes linearly with the change of the surface temperature of the metal bracket. Therefore, ensuring the stability of the surface temperature of the metal bracket is considered to ensure the stability of the preset working temperature of the scintillator. Since the efficiency of heat conduction is much greater than that of thermal radiation and heat convection, the heat conduction relationship between the surface temperature of the metal bracket and the preset working temperature of the scintillator is specifically introduced below:

[0054] Assume that the temperature of the contact surface between the metal bracket and the heating resistor is T0°C, the preset working temperature of the scintillator is T1°C, the steady-state temperature of the air in the detection device is T2°C, the area of ​​the scintillator is A, and the wall thickness of the metal bracket is b;

[0055] According to Newton's cooling law, the heat dissipation of the scintillator is Q 散 =h*(T2-T1)*A;

[0056] According to the heat conduction equation, the heat absorbed by the scintillator is Q 吸 =λ*(T0-T1)*A / b;

[0057] Thermal equilibrium Q 散 =Q 吸 , according to h*(T2-T1)*A=λ*(T0-T1)*A / b:

[0058]

[0059] Wherein, h is the convection heat transfer coefficient of the scintillator surface, unit is W / (m^2.K), and λ is the thermal conductivity of the metal bracket.

[0060] Since T2 is usually a constant value, the stability of T0 can be ensured by adjusting the heating resistor, that is, T1 can be kept stable.

[0061] The control module 20 is disposed on the base of the base 10 and is used to control the heating resistor 341 and the temperature sensor 342 . Figure 4 The schematic diagram of the working principle of the control module, the heating resistor and the temperature sensor is shown in FIG. Figure 4 As shown, the control module 20 includes a processing unit 21 and a pulse width modulation circuit 22. The processing unit 20 includes an acquisition circuit 211 and an operator 212. The acquisition circuit 211 is electrically connected to the temperature sensor and is used to receive the temperature signal of the metal bracket sent by the temperature sensor. The operator 212 is used to receive the real-time temperature signal of the surface of the metal bracket sent by the acquisition circuit and convert it into the current temperature of the scintillator through the above formula (1).

[0062] The pulse width modulation circuit 22 is electrically connected to the heating resistor 341 and is also connected to the operator 212 in the processing unit 20, and is used to control the heating power of the heating resistor according to the current temperature of the scintillator to generate compensation heat. The pulse width modulation circuit can accurately control the input voltage of the heating resistor to change within a very small fluctuation range. Assuming that the rated effective heating power of a heating resistor is 10W, by using the pulse width modulation circuit, the duty cycle of the input voltage can be adjusted to control the effective heating power to any value of 0-10W, thereby adjusting the compensation heat in real time. Specifically, when the current temperature of the scintillator is lower than the preset operating temperature, there is a compensation temperature at this time, which is the difference between the preset operating temperature and the current temperature. By controlling the pulse width of the pulse width signal output by the pulse width modulation circuit to the heating resistor, the effective heating power of the heating resistor corresponds to the compensation temperature, and finally the scintillator reaches the preset operating temperature.

[0063] In the present invention, the applicant has found that the CT detection device with the above structure can control the real-time temperature difference of the scintillator to be within ±0.2°C when it is in a stable state by controlling the sum of the sampling period, operation time, and output delay to be less than the temperature change integration time, wherein the sampling period refers to the frequency design of sampling using the temperature sensor (microsecond level), the operation time refers to the time (millisecond level) for the operator to calculate and output the pulse width waveform according to the temperature change internally, and the output delay refers to the delay (nanosecond level) for the pulse width modulation circuit to send the pulse width signal to the heating resistor; the integration time of the temperature change refers to the temperature sensor collecting multiple data within tens of milliseconds (ms), and defining its temperature by the integral method is closer to the true value. It can be understood that the integration time of the temperature change is the average temperature in a certain time period. In this embodiment, the time of adding up the sampling period, operation time, and output delay is ms level, and is less than the temperature change integration time of 10ms level. Optionally, since the physical property stability of most scintillators within ±0.5°C is sufficient for the stability of the imaging system, and in order to accommodate installation and manufacturing errors, the steady-state real-time temperature difference is controlled within ±0.5°C in actual applications.

[0064] In other optional embodiments, the closed-loop heating unit can be used for the self-heating climbing stage of the conversion unit, that is, the process of the conversion unit heating up from the current room temperature to the preset operating temperature. Compared with the heating of the conversion unit through self-heating, it can accelerate the self-heating speed and further improve the scanning efficiency.

[0065] In other optional embodiments, the CT detection device further includes a housing (not shown) and a fan (not shown) disposed on the housing. The housing is matched with the outer wall of the base, the scintillator is exposed through the housing, and the housing is used to protect the detector module and further prevent dust from entering the internal space. The shape of the housing is adapted to the shape of the base, and is not limited here.

[0066] The fan is arranged on the housing, facing the detector module, and electrically connected to the control module. It is used to turn on when the external temperature of the detection device rises sharply, increase the heat dissipation of the internal space of the detection device, and form a new steady state. Specifically, when the external environmental temperature rises sharply, the self-heating of the conversion unit will be higher than the preset working temperature. At this time, the fan is turned on to cool the inside of the detection device to the preset working temperature. It can be understood that when the external environmental temperature is stable and the detection device is working normally, the fan does not work, which can reduce the fan operating frequency and improve the dustproof effect inside the detector.

[0067] A CT detection device provided in this embodiment adopts a distributed closed-loop heating unit. The self-heat of the conversion unit is combined with the heat of the closed-loop heating unit to stabilize the scintillator temperature of the CT detection device, which can improve the quality of the scanned image. In addition, the CT detection device fully utilizes the energy of the self-heating of the conversion unit to reduce energy loss. Finally, the real-time temperature difference when the detection device is in a steady state is controlled to ±0.5°C, which greatly reduces the requirements for the temperature characteristics of the scintillator, and the purity and processing technology of the mainstream scintillator material can be greatly relaxed, thereby reducing the cost of the scintillator while ensuring the image quality.

[0068] Example 2

[0069] Based on the CT detection device provided in the above embodiment, Embodiment 2 of the present invention further provides a temperature control method of the above CT detection device, such as Figure 5 As shown, the method specifically includes:

[0070] S10, when the spontaneous heat generated by the conversion unit causes the scintillator to reach a preset operating temperature, the surface temperature of the metal bracket is collected in real time;

[0071] In this step, the temperature sensor collects the surface temperature of the metal bracket in real time and transmits it to the control module.

[0072] S20, if the surface temperature of the metal bracket is lower than the preset working temperature, controlling the closed-loop heating unit to work and transferring the generated heat to the scintillator through the metal bracket;

[0073] In this step, during the operation of the closed-loop heating unit, the heat generated by the closed-loop heating unit is simultaneously transmitted to the scintillator and the conversion unit, so that the self-heat of the conversion unit reaches a preset operating temperature, and the temperature of the scintillator reaches the preset operating temperature, and the temperature reaches a equilibrium state.

[0074] S30, when the real-time temperature of the scintillator reaches the preset operating temperature, the closed-loop heating unit is controlled to stop working, and at this time the conversion unit transfers the self-generated heat to the scintillator to maintain it at the preset operating temperature.

[0075] In this step, the closed-loop heating unit does not work all the time, but only acts as a compensation means when the self-heat of the conversion unit cannot maintain the preset working temperature of the scintillator, and increases the temperature of the scintillator to reach the preset working temperature, so as to be in a balanced state. In other words, once the temperature of the scintillator reaches the preset working temperature, the closed-loop heating unit stops working, and relies on the self-heat of the conversion unit to maintain the balanced state, and this is repeated.

[0076] In other optional embodiments, before step S10, the method further includes:

[0077] In the process of the conversion unit generating self-heat, the closed-loop heating unit is controlled to work and transmit the generated heat to the conversion unit until the self-heat of the conversion unit reaches the preset working temperature of the scintillator, at which time the closed-loop heating unit stops working. This step can shorten the self-heating time of the conversion unit and improve the detection efficiency.

[0078] In other optional embodiments, the method further includes:

[0079] S40, when the real-time temperature of the scintillator exceeds the preset operating temperature, control the fan to turn on to reduce the temperature of the scintillator to the preset operating temperature.

[0080] For other specific contents of this embodiment, please refer to the description in Embodiment 1, which will not be repeated here.

[0081] Finally, a temperature control method for a CT detection device provided in an embodiment of the present invention adopts a distributed heating scintillator, and stabilizes the temperature of the scintillator by controlling the closed-loop heating unit compensation temperature, thereby improving the quality of the scanned image; in addition, the energy of the self-heating of the conversion unit is fully utilized to reduce energy loss; finally, the real-time temperature difference is controlled at ±0.5°C when the detection device is in a steady state, which greatly reduces the requirements for the temperature characteristics of the scintillator, and the purity and processing technology of the mainstream scintillator material can be greatly relaxed, thereby reducing the cost of the scintillator while ensuring image quality.

[0082] The specific implementation methods described above further illustrate the objectives, technical solutions and beneficial effects of the present invention in detail. It should be understood that the above description is only a specific implementation method of the present invention and is not intended to limit the scope of protection of the present invention. Any modifications, equivalent substitutions, improvements, etc. made within the spirit and principles of the present invention should be included in the scope of protection of the present invention.

Claims

1. A CT detection device, characterized in that: It includes a base, a control module arranged on the base, and a plurality of detection modules, each detection module including: A metal bracket, the metal bracket is fixed to the base; a scintillator and a conversion unit connected to the scintillator, wherein the scintillator and the conversion unit are arranged on the same surface of the metal bracket opposite to each other, the scintillator is exposed outside the base and is used to receive X-rays, and the conversion unit is used to process the X-rays; A closed-loop heating unit, which is disposed on a surface of the metal bracket away from the scintillator and is electrically connected to the control module, and is used to adjust the current temperature of the scintillator to maintain it at the preset working temperature when the self-heat of the conversion unit cannot maintain the scintillator at the preset working temperature; The closed-loop heating unit comprises a heating resistor and a temperature sensor, wherein the heating resistor and the temperature sensor are both arranged on a surface of the metal bracket away from the scintillator and are electrically connected to the control module respectively; Wherein, the temperature sensor is used to collect the real-time temperature of the surface of the metal bracket; the control module controls the heating resistor to generate heat according to the real-time temperature of the surface of the metal bracket, and the heat is transmitted to the scintillator through the metal bracket; The heating resistor is a thin film thermal resistor, which is pasted on the surface of the metal bracket; The metal bracket is a sheet-like structure, and is used to transfer the self-heat of the conversion unit and the heat generated by the closed-loop heating unit to the scintillator.

2. The detection device according to claim 1, characterized in that: The control module includes a pulse width modulation circuit, which is used to control the power of the heating resistor to generate heat.

3. The detection device according to claim 1, characterized in that: The control module further includes a processing unit, which is used to receive the real-time temperature of the metal support surface collected by the temperature sensor, and obtain the current temperature of the scintillator according to the real-time temperature of the metal support surface.

4. The detection device according to claim 3, characterized in that: The temperature of the scintillator changes linearly with the change of the real-time temperature of the surface of the metal support.

5. The detection device according to claim 1, characterized in that: When the scintillator is in equilibrium, the real-time temperature difference is within ±0.5°C.

6. A temperature control method for a CT detection device according to any one of claims 1 to 5, characterized in that: include: When the spontaneous heat generated by the conversion unit makes the scintillator reach the preset working temperature, the surface temperature of the metal bracket is collected in real time; If the surface temperature of the metal bracket is lower than the preset working temperature, the closed-loop heating unit is controlled to work, and the generated heat is transferred to the scintillator through the metal bracket; When the real-time temperature of the scintillator reaches the preset operating temperature, the closed-loop heating unit is controlled to stop working. At this time, the conversion unit transfers the self-generated heat to the scintillator to maintain it at the preset operating temperature.

7. The method according to claim 6, characterized in that The method further comprises: In the process of the conversion unit generating self-heat, the closed-loop heating unit is controlled to work and transfer the generated heat to the conversion unit until the self-heat of the conversion unit reaches the preset operating temperature of the scintillator, at which time the closed-loop heating unit stops working.

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