Constant heat radiation device, infrared biological activity tester and use method of infrared biological activity tester

Abstract

The invention relates to a constant thermal radiation device, an infrared biological activity tester and a use method thereof, the constant thermal radiation device comprises a temperature adjusting layer, the temperature adjusting layer comprises a plurality of heating structures and a plurality of cooling structures, and at least one heating structure is adjacent to at least one cooling structure. According to the technical scheme, the constant heat radiation device can be suitable for serving as a background of the subject matter to be detected, the heat radiation quantity of the heat radiation layer can be adjusted under the action of the heating structure and the cooling structure until the heat radiation quantity is consistent with the reference heat radiation quantity, and then the heat radiation quantity is compared with the heat radiation quantity of the subject matter to be detected; the temperature sensor is used for collecting temperature data of a subject matter to be detected, for example, the subject matter to be detected can be human tissue or in-vitro tissue, and the activity of the human tissue or in-vitro tissue can be evaluated through the temperature data so as to judge the health condition. The heat radiation quantity of the heat radiation layer is adjusted through the cooperative effect of the adjacent heating structure and cooling structure, and the adjusting efficiency and stability are good.

Description

Technical Field

[0001] The present disclosure relates to the technical field of medical devices, and in particular to a constant heat radiation device, an infrared bioactivity meter and a method of using the same. Background Art

[0002] Infrared imaging technology can use the body's own thermal radiation for imaging. It does not come into contact with the body during the examination, so as to achieve non-destructive, non-contact, and painless detection. The imaging speed is relatively fast. Then, the infrared thermal map distribution and temperature difference information obtained are used to determine whether the blood vessels have lesions and whether the functions of human organs and tissues are normal. The overall examination is accurate and fast.

[0003] In the related art, infrared imaging requires a thermal image acquisition and positioning background device to provide a constant temperature background, but the ability to maintain and adjust the constant temperature background is poor. Summary of the Invention

[0004] The purpose of the present disclosure is to provide a constant heat radiation device, an infrared bioactivity meter and a method of using the same, which at least have good constant temperature environment maintenance and temperature regulation capabilities, so as to at least partially solve the above technical problems.

[0005] In order to achieve the above-mentioned purpose, according to the first aspect of the present disclosure, a constant heat radiation device is provided, comprising a temperature regulating layer and a heat radiation layer arranged above the temperature regulating layer, the temperature regulating layer being used to regulate the temperature of the heat radiation layer, the temperature regulating layer comprising a plurality of heating structures and a plurality of cooling structures, at least one of the heating structures being arranged adjacent to at least one of the cooling structures.

[0006] Optionally, the thermal radiation layer has the same emissivity as the object to be detected.

[0007] Optionally, the multiple heating structures and the multiple cooling structures are arranged in rows and columns, and along the row direction and the column direction, at least one cooling structure is provided between two adjacent heating structures, or at least one heating structure is provided between two adjacent cooling structures.

[0008] Optionally, the temperature adjustment layer further includes a heat conducting structure, and the heat conducting structure is arranged between the temperature increasing structure and the temperature decreasing structure for heat conduction.

[0009] Optionally, the heating structure includes carbon nanotubes suitable for electric current heating, and the cooling structure includes a cooling pipeline suitable for circulating a cooling medium. wherein the carbon nanotubes are treated by plasma; and / or A protective layer is provided on the carbon nanotubes.

[0010] Optionally, it also includes a temperature control layer arranged below the temperature adjustment layer, the temperature control layer includes a base member, and the base member is provided with a conductive circuit, a temperature sensor and a temperature controller, the conductive circuit is suitable for connecting the carbon nanotubes, the temperature sensor is suitable for monitoring the temperature of the heat radiation layer, and the temperature controller signal is connected to the temperature sensor and is used to control the on and off of the conductive circuit.

[0011] Optionally, a heat insulation layer is further included, and the heat insulation layer is arranged on the side of the temperature control layer away from the temperature adjustment layer, or The heat insulation layer is arranged on a side of the temperature control layer away from the temperature adjustment layer, and on each circumferential side of the temperature control layer and the temperature adjustment layer.

[0012] According to the second aspect of the present disclosure, an infrared bioactivity meter is provided, which is suitable for detecting a target object to be detected, and includes the above-mentioned constant thermal radiation device and an imaging element arranged opposite to the constant thermal radiation device, and the imaging element is used to detect the target object to be detected between the imaging element and the constant thermal radiation device.

[0013] Optionally, the constant heat radiation devices and the imaging elements are arranged in multiple groups and are arranged around the target to be detected, and the imaging element is connected to a constant heat radiation device arranged opposite to the constant heat radiation device in the same group.

[0014] Optionally, the imaging element can selectively capture near infrared light, mid infrared light, or far infrared light.

[0015] Optionally, the imaging element includes an optical lens and a plurality of infrared detectors arranged in an array.

[0016] According to a third aspect of the present disclosure, a method for using an infrared bioactivity meter is provided, which is applicable to the above-mentioned infrared bioactivity meter. The method comprises: Providing the above-mentioned constant heat radiation device; adjusting the heat radiation amount of the heat radiation layer of the constant heat radiation device to be the same as the reference heat radiation amount; placing the object to be detected above the constant heat radiation device; A thermal radiation image of the target object to be detected is obtained through the imaging element.

[0017] Through the above technical solution, the constant heat radiation device can be suitable as a background for the target to be detected. Under the action of the heating structure and the cooling structure, the temperature of the heat radiation layer can be adjusted so that the temperature of the heat radiation layer remains consistent with the reference temperature and is compared with the temperature of the target to be detected for use in temperature data collection of the target to be detected. The number of heating structures and cooling structures is set to multiple, and at least one heating structure is arranged adjacent to at least one cooling structure, so that the temperature of the heat radiation layer can be adjusted through the cooperation of the adjacent heating structures and cooling structures, and the temperature maintenance stability is better.

[0018] Other features and advantages of the present disclosure will be described in detail in the following detailed description. BRIEF DESCRIPTION OF THE DRAWINGS

[0019] The accompanying drawings are used to provide a further understanding of the present disclosure and constitute a part of the specification. Together with the following detailed description, they are used to explain the present disclosure but do not constitute a limitation of the present disclosure. In the accompanying drawings: Figure 1 1 is a schematic diagram of the overall structure of an infrared bioactivity meter provided by an exemplary embodiment of the present disclosure; Figure 2 is a schematic structural diagram of a temperature adjustment layer provided in an exemplary embodiment of the present disclosure; Figure 3 is a schematic cross-sectional view of a constant heat radiation device provided by an exemplary embodiment of the present disclosure; Figure 4 2 is a schematic structural diagram of an imaging element provided by an exemplary embodiment of the present disclosure.

[0020] Description of Reference Numerals 10. Constant heat radiation device; 1. Temperature adjustment layer; 11. Heating structure; 12. Cooling structure; 13. Heat conduction structure; 2. Heat radiation layer; 3. Temperature control layer; 31. Base member; 32. Conductive circuit; 33. Temperature sensor; 34. Temperature controller; 4. Heat insulation layer; 20. Imaging element; 201. Optical lens; 202. Infrared detector. DETAILED DESCRIPTION

[0021] The following describes the specific embodiments of the present disclosure in detail with reference to the accompanying drawings. It should be understood that the specific embodiments described herein are only used to illustrate and explain the present disclosure and are not intended to limit the present disclosure.

[0022] In this disclosure, unless otherwise specified, "inside" and "outside" refer to the inside and outside of the corresponding component's outline; "far" and "near" refer to the spatial distance of the corresponding component relative to another component. Furthermore, the terms "first," "second," and so on, used in this disclosure, are intended to distinguish one element from another and do not convey sequential or significant meanings. In the following description, unless otherwise indicated, identical numerals in different figures represent identical or similar elements.

[0023] According to the first aspect of the present disclosure, referring to Figures 1 to 4 The present disclosure provides a constant heat radiation device 10, comprising a temperature regulating layer 1 and a heat radiation layer 2 disposed above the temperature regulating layer 1. The temperature regulating layer 1 is used to regulate the temperature of the heat radiation layer 2 to change the heat radiation amount of the heat radiation layer 2. The temperature regulating layer 1 comprises a plurality of heating structures 11 and a plurality of cooling structures 12, wherein at least one heating structure 11 is disposed adjacent to at least one cooling structure 12. The above description and the following description of the above description and the following description of the above description may refer to Figure 1 shown.

[0024] Through the above technical solution, the constant heat radiation device 10 can be suitable as a background for the target to be detected. Under the action of the heating structure 11 and the cooling structure 12, the temperature of the heat radiation layer 2 can be adjusted so that the heat radiation amount of the heat radiation layer 2 is consistent with the reference heat radiation amount, and compared with the heat radiation amount of the target to be detected, so as to be used for collecting temperature data of the target to be detected. For example, the target to be detected can be human tissue or ex vivo tissue. The activity of the human tissue or ex vivo tissue can be evaluated through the temperature data to determine the health status. In particular, the number of heating structures 11 and cooling structures 12 is set to be multiple, and at least one heating structure 11 is arranged adjacent to at least one cooling structure 12, so that the heat radiation amount of the heat radiation layer 2 can be adjusted through the cooperation of the adjacent heating structures 11 and cooling structures 12, and the stability of maintaining a constant heat radiation amount is better.

[0025] In an exemplary application scenario, the target object to be detected can be human tissue or ex vivo tissue, and the activity of the human tissue or ex vivo tissue needs to be detected to determine whether the human tissue is healthy and for ex vivo organ preservation and transplantation. At this time, the constant thermal radiation device 10 can serve as the background of the human tissue or ex vivo tissue to be detected to provide a background reference standard for the thermal radiation amount. In this way, through the combined action of the heating structure 11 and the cooling structure 12, the thermal radiation amount of the thermal radiation layer 2 is adjusted to be consistent with the reference thermal radiation amount and dynamically maintained, and then the human tissue or ex vivo tissue is placed above the constant thermal radiation device 10. For example, infrared imaging technology can be used to collect data on the thermal radiation amount of the human tissue or ex vivo tissue, so as to quantify its physiological function and metabolic state and determine its activity by detecting the difference in infrared radiation generated by the metabolic activity of the tissue or cell. Among them, living tissues will form local temperature gradients due to metabolic heat production (such as cellular respiration, blood perfusion) or pathological conditions (such as inflammation, tumor angiogenesis). Infrared imaging technology can capture these temperature changes non-contactly and convert them into thermal images to reflect thermal radiation data, thereby indirectly reflecting biological activity.

[0026] It can be understood that by using the constant thermal radiation device 10 as the background of the target to be detected and adjusting the thermal radiation amount of the thermal radiation layer 2 to be consistent with the reference thermal radiation amount, it is possible to narrow the temperature detection range, that is, the range between the reference temperature and the temperature of the target to be detected, thereby improving detection sensitivity. This is reflected in the reduction of the temperature difference between the color gradients in infrared imaging. The reference thermal radiation amount can be adjusted to suit different targets to be detected.

[0027] Based on this, the present disclosure provides an infrared bioactivity meter suitable for quantifying the activity of the aforementioned target to be detected. The infrared bioactivity meter includes the aforementioned constant thermal radiation device 10 and an imaging element 20 disposed opposite the constant thermal radiation device 10, with the target to be detected located between the constant thermal radiation device 10 and the imaging element 20. Taking the target to be detected as human hand tissue as an example, the imaging element 20 can image the changes in the thermal radiation amount of the hand tissue caused by metabolic heat production and blood flow. The thermal radiation amount of the hand tissue is compared with the thermal radiation layer 2 of the constant thermal radiation device 10. Using the reference thermal radiation amount as a reference standard, the thermal radiation amount at various locations of the hand tissue and the thermal radiation amount difference can be obtained. The obtained thermal radiation amount data can then be analyzed to determine the health status of the hand tissue.

[0028] Therefore, the above-mentioned infrared bioactivity meter provides a non-invasive, real-time activity quantification tool for clinical surgical navigation (such as tissue perfusion assessment, tumor localization, and vascular anastomosis verification) and basic research (ex vivo organ preservation and cell activity analysis). Its unique thermal sensitivity is particularly suitable for screening superficial lesions and scenarios with special interference (such as optically transparent tissue research).

[0029] It is understood that during the collection of thermal radiation data for the aforementioned objects to be detected, the reference thermal radiation may be adjusted. For example, for ex vivo limb replantation, the activity of the ex vivo limb must be tested during preparation. To ensure the activity of the ex vivo limb, it is typically refrigerated at a relatively low temperature (0-4°C). Therefore, when the activity of the ex vivo limb is tested, the reference thermal radiation decreases. In this case, the cooling structure 12 can be used to reduce the thermal radiation of the thermal radiation layer 2 of the constant thermal radiation device 10. Correspondingly, when the activity of human tissue is tested, the reference thermal radiation increases (the reference temperature can be 20-30°C). In this case, the heating structure 11 can be used to increase the thermal radiation of the thermal radiation layer 2 of the constant thermal radiation device 10.

[0030] Therefore, during the aforementioned process of adjusting the reference thermal radiation amount, the heating structure 11 and the cooling structure 12 can cooperate. For example, when the heating structure 11 increases the thermal radiation amount of the thermal radiation layer 2, when the thermal radiation amount approaches the reference thermal radiation amount, the cooling structure 12 can cooperate to adjust the thermal radiation amount of the thermal radiation layer 2, thereby improving the accuracy of adjusting the thermal radiation amount and maintaining stability. Similarly, when the cooling structure 12 decreases the thermal radiation amount of the thermal radiation layer 2, when the thermal radiation amount approaches the reference thermal radiation amount, the heating structure 11 can cooperate to adjust the thermal radiation amount of the thermal radiation layer 2, thereby improving the accuracy of adjusting the thermal radiation amount and maintaining stability.

[0031] In some embodiments, the emissivity of thermal radiation layer 2 and the object to be detected can be the same. Emissivity is a physical quantity that describes the ability of a material surface to emit thermal radiation at a specific temperature and wavelength. It is defined as the ratio of the actual radiant flux emitted by the material to the radiant flux emitted by an ideal blackbody at the same temperature. Taking the surface of human tissue as an example, the emissivity is 0.95-0.98. Therefore, when performing infrared imaging on human tissue, the emissivity of thermal radiation layer 2 can be set to the same as that of the human tissue, and the thermal radiation amount of thermal radiation layer 2 can be used as a reference to reflect the absolute thermal radiation amount of the human tissue. That is, in infrared imaging, the thermal radiation amount of human tissue that has the same color as thermal radiation layer 2 is equal to the reference thermal radiation amount. Therefore, the thermal radiation amount of each part of the human tissue and the thermal radiation gradient can be intuitively detected.

[0032] Illustratively, the material of the heat radiation layer 2 may be a water-containing polymer (such as hydrogel) or silicon carbide, silicon nitride ceramics, etc., but the present disclosure is not limited thereto.

[0033] It can be understood that the material of the thermal radiation layer 2 can be adaptively adjusted for different targets to be detected, so that the thermal radiation layer 2 can be placed only above the temperature adjustment layer 1, that is, the thermal radiation layer 2 is arranged between the target to be detected and the temperature adjustment layer 1. At this time, the heating structure 11 and the cooling structure 12 adjust the thermal radiation amount of the thermal radiation layer 2 through heat exchange.

[0034] In addition, the emissivity of the thermal radiation layer 2 may also be different from the emissivity of the target object to be detected, and may be calibrated through surface treatment or subsequent procedures or algorithms to obtain thermal radiation data.

[0035] In some embodiments, reference Figure 2 As shown, multiple heating structures 11 and multiple cooling structures 12 can be arranged in rows and columns. Along the row direction and the column direction, at least one cooling structure 12 is provided between two adjacent heating structures 11, and at least one heating structure 11 is provided between two adjacent cooling structures 12. The present disclosure exemplarily arranges the heating structures 11 and the cooling structures 12 alternately along the row direction and the column direction. In this way, when viewed from top to bottom along a direction perpendicular to the temperature adjustment layer 1, the multiple heating structures 11 and the multiple cooling structures 12 are arranged in an array, and the cooling structures 12 are provided circumferentially around the heating structures 11, and the cooling structures 12 are provided circumferentially around the cooling structures 12, so that the heating structures 11 and the cooling structures 12 can cooperate with each other.

[0036] In some other embodiments, when viewed from top to bottom perpendicular to the temperature adjustment layer 1, multiple heating structures 11 and multiple cooling structures 12 can be nested, wherein both the heating structures 11 and the cooling structures 12 are arranged in an annular shape, and the heating structures 11 and the cooling structures 12 are alternately arranged radially. It is understood that the multiple heating structures 11 and the multiple cooling structures 12 can also be arranged in any other suitable manner, and the present disclosure is not limited thereto.

[0037] In some embodiments, reference Figure 2 and Figure 3 As shown, the temperature adjustment layer 1 may further include a heat-conducting structure 13, which is arranged between the heating structure 11 and the cooling structure 12 for heat conduction. In this way, the filling effect of the heat-conducting structure 13 can balance the temperature distribution, improve the accuracy of temperature regulation of the heat radiation layer 2 and the stability of temperature maintenance, and improve the accuracy of heat radiation amount regulation of the heat radiation layer 2 and the stability of heat radiation amount maintenance.

[0038] The heat-conducting structure 13 can comprise a composite material of aluminum nitride and graphene. Both aluminum nitride and graphene have high thermal conductivity, enabling rapid heat transfer between the heating structure 11 and the cooling structure 12 while reducing contact thermal resistance and avoiding local hot spots. Furthermore, the heat-conducting structure 13 can be used to flexibly adapt the heating structure 11 and the cooling structure 12, providing a flexible transition and enhancing thermal contact.

[0039] In addition, the heat conducting structure 13 may also be a composite material of boron nitride and graphene, a composite material of silicon nitride and graphene, or a composite material of metal matrix and graphene, etc., but the present disclosure is not limited thereto.

[0040] In some embodiments, the temperature-raising structure 11 may include carbon nanotubes suitable for electric current heating, wherein the carbon nanotubes have excellent electrical conductivity (high conductivity), controllable temperature coefficient of resistance (which is conducive to stabilizing power output at high temperatures and avoiding overheating runaway), flexibility and processability (adaptable to bending and not easy to break), and have both high performance and multifunctionality during the electric heating process. In addition, in practical applications, the conductivity, durability and processability can be further optimized through composite modification (such as combination with metals, ceramics or polymers).

[0041] Among them, carbon nanotubes are treated with plasma. For example, nitrogen plasma treatment can be used to enhance the temperature sensitivity of the resistor and improve temperature control accuracy. The carbon nanotubes are first cleaned to remove impurities such as organic matter adsorbed on the surface, metal catalyst residues, or amorphous carbon. Common methods include acid treatment, solvent ultrasonic dispersion, or high-temperature annealing to evenly disperse the carbon nanotubes on a substrate (such as a silicon wafer or ceramic wafer), or using fluidized beds, aerosols, etc. to uniformly expose them in the plasma area to avoid agglomeration and uneven treatment. Radio frequency, direct current, or microwave plasma equipment is used, using high-purity nitrogen as the working gas (purity ≥99.99%). In some scenarios, argon can be mixed in to adjust the plasma activity. In addition, a protective layer can be provided on the carbon nanotubes. Medical-grade polyparaxylene (Parylene HT) can be sprayed on the carbon nanotubes to enhance water resistance and corrosion resistance.

[0042] Furthermore, the cooling structure 12 may include cooling pipes adapted to circulate a cooling medium. The cooling pipes may be externally connected to the cooling medium, and the interface may be provided on the aforementioned heat-conducting structure 13. The cooling medium may be cooling water or other coolant, and this disclosure does not specifically limit this. It is understood that the carbon nanotubes and cooling pipes may be arranged in a spiral arrangement perpendicular to the temperature-regulating layer 1 to enhance temperature regulation capabilities.

[0043] In some embodiments, reference Figure 3As shown, the constant heat radiation device 10 also includes a temperature control layer 3 arranged below the temperature adjustment layer 1. The temperature control layer 3 may include a base member 31, on which a conductive circuit 32, a temperature sensor 33 and a temperature controller 34 are provided. The conductive circuit 32 is suitable for connecting to the carbon nanotubes so as to pass current into the carbon nanotubes to heat and increase the temperature of the heat radiation layer 2. The temperature sensor 33 is suitable for monitoring the temperature of the heat radiation layer 2. The temperature controller 34 is connected to the temperature sensor 33 by signal and is used to control the on and off of the conductive circuit 32.

[0044] For example, the substrate 31 can be constructed as a circuit board, with an insulating layer (such as a ceramic substrate or polyimide) added between the conductive traces 32 and the heating / sensing structure to meet insulation requirements. Platinum nanowires (Pt NWs) can serve as temperature sensors 33 (Pt has a stable resistance-temperature coefficient). A PID (Proportion Integration Differentiation) controller can be used for precise temperature control. The PID controller can be remotely controlled via a wireless communication module to adjust the reference thermal radiation level.

[0045] Furthermore, a redundant heating structure can be provided, such as a serpentine arrangement of Au (gold) / Ti (titanium) electrodes. When current passes through the Au / Ti electrodes, electrical energy is converted into heat. The Au layer, with its high conductivity, serves as the main conductor and dominates current flow. The Ti layer acts as an adhesion layer, bonding to the substrate and introducing a certain resistance to regulate overall heating power. It is understood that the Au / Ti electrodes can also be connected to the aforementioned conductive traces 32. If the carbon nanotubes fail due to aging or poor contact, the Au / Ti electrodes can take over the heating function, avoiding downtime.

[0046] In some embodiments, reference Figure 1 and Figure 3 As shown, the constant heat radiation device 10 further includes a thermal insulation layer 4, which is disposed on the side of the temperature control layer 3 facing away from the temperature adjustment layer 1, or alternatively, on the side of the temperature control layer 3 facing away from the temperature adjustment layer 1, as well as on all circumferential sides of the temperature control layer 3 and the temperature adjustment layer 1. Thus, the thermal insulation layer 4 reduces the impact of the external ambient temperature and reduces heat loss, thereby improving the efficiency of regulating the amount of heat radiation. Furthermore, the outer layer of the thermal insulation layer 4 can be made of copper foil to reflect external electromagnetic interference (such as radio frequency signals), thereby reducing interference with the current flowing through the carbon nanotubes and with the temperature sensor 33 and temperature controller 34.

[0047] According to the second aspect of the present disclosure, Figure 1As shown, the present disclosure provides an infrared bioactivity meter suitable for quantifying the activity of the above-mentioned target to be detected. The infrared bioactivity meter includes the above-mentioned constant thermal radiation device 10 and an imaging element 20 arranged opposite to the constant thermal radiation device 10. The imaging element 20 is used to detect the target to be detected between the constant thermal radiation device 10 and the imaging element 20.

[0048] Taking the human hand tissue as an example, the imaging element 20 can image the changes in the thermal radiation amount of the hand tissue caused by metabolic heat generation and blood flow. The thermal radiation amount of the hand tissue is compared with the thermal radiation amount of the thermal radiation layer 2 of the constant thermal radiation device 10. With the reference thermal radiation amount as the reference standard, the thermal radiation amount at various locations of the hand tissue and the thermal radiation amount difference can be obtained. The obtained thermal radiation amount data is then analyzed to determine the health status of the hand tissue.

[0049] For example, tissue perfusion can be quantified using acquired thermal radiation data to assess health status. Tissue perfusion refers to the dynamic process by which blood, through the capillary system, delivers oxygen and nutrients to tissue cells and removes metabolic waste. It is a core mechanism for maintaining organ function and cell survival, and is closely related to the diagnosis, treatment, and prognosis of various diseases. Its core goal is to assess whether microcirculatory blood flow is adequate and whether tissue cells are receiving sufficient oxygen and nutrients.

[0050] For example, still using human hand tissue as an example, the proximal artery of the hand tissue can be compressed using, for example, a mercury sphygmomanometer. Continuous image capture of the hand tissue is then performed using the imaging element 20. Once no significant image changes are observed, arterial perfusion of the hand tissue is completely blocked. The sphygmomanometer pressure is then rapidly released, and image capture continues until the hand tissue is fully perfused. By comparing the images with normal values, the tissue perfusion status can be assessed. Metabolic status is primarily monitored by measuring the time it takes for the tissue to be fully perfused and the amount of thermal radiation during the perfusion process.

[0051] In some embodiments, the constant heat radiation devices 10 and imaging elements 20 can be arranged in multiple groups and arranged around the target to be detected, and the imaging elements 20 can be connected to the constant heat radiation devices 10 arranged opposite to the constant heat radiation devices 10 in the same group. In this way, by providing multiple groups of constant heat radiation devices 10 and imaging elements 20, the target to be detected can be detected from multiple angles to obtain heat radiation data of the target to be detected at multiple angles. Then, the above-mentioned multiple heat radiation data can be fitted through a program or algorithm, for example, to obtain three-dimensional stereoscopic images and temperature data of the target to be detected, which facilitates the assessment of the activity of the target to be detected.

[0052] It is understood that, illustratively, the constant heat radiation device 10 and the imaging element 20 can be set as four groups and arranged around the target to be detected to form an annular structure. The two axial sides of the annular structure can be closed to reduce the influence of the external environment, such as visible light. Of course, one side can be provided with an opening to accommodate the entry of the target to be detected. The constant heat radiation device 10 can be used to close the annular structure so as to form an internal constant heat radiation environment. The constant heat radiation device 10 located below the target to be detected and the imaging element 20 located above the target to be detected are set in the same group, and the constant heat radiation device 10 located above the target to be detected and the imaging element 20 located below the target to be detected are set in the same group.

[0053] In addition, the imaging structure can be connected to the constant thermal radiation device 10 that is arranged opposite to the constant thermal radiation device 10 in the same group in any appropriate manner. For example, the imaging structure can be embedded in the thermal radiation layer 2 of the constant thermal radiation device 10 and fixed to the thermal radiation layer 2 by, for example, bonding, so as not to affect the constant thermal radiation device 10 as a background reference for the thermal radiation amount of the imaging element 20 on the opposite side. The present disclosure does not make any specific restrictions on this.

[0054] It can be understood that the number of constant thermal radiation devices 10 and imaging elements 20 can be set to two groups, for example, they can be arranged above and below the target to be detected respectively, or the number of constant thermal radiation devices 10 and imaging elements 20 can be set to three groups, five groups or more groups, etc., and the present disclosure is not limited to this.

[0055] In some embodiments, the imaging element 20 can selectively capture near-infrared light, mid-infrared light, or far-infrared light. It will be appreciated that near-infrared light, mid-infrared light, and far-infrared light have different penetration depths. Near-infrared light has a higher penetration depth and is suitable for deep tissue detection in living organisms, such as tissue oxygenation monitoring. Mid-infrared light has a shallower penetration depth and is suitable for component analysis. Far-infrared light has an extremely shallow penetration depth and is suitable for detecting abnormal surface temperatures. Thus, by capturing infrared light of different wavelengths, different parts of the target object can be analyzed, thereby increasing the detection range.

[0056] In some embodiments, reference Figure 4As shown, the imaging element 20 may include an optical lens 201 and a plurality of infrared detectors 202 arranged in an array, wherein the infrared detector 202 may be a photon detector based on quantum effects and a thermal detector based on thermal effects, and a two-dimensional detector array (such as 320×240, 640×512 pixels) is used. Each pixel corresponds to a sensor unit, and infrared radiation from different positions in the scene is received simultaneously to form infrared image data. The sensor of each pixel converts infrared energy into an electrical signal (voltage or current), which is collected and amplified by a readout circuit (ROIC), and then converted into a digital signal through an analog-to-digital converter (ADC). The electrical signal intensity is mapped to a temperature value, which is usually displayed in pseudo-color (such as rainbow color, iron red), with high-temperature areas corresponding to bright colors and low temperatures corresponding to dark colors. The processed digital signal drives a display (such as LCD, OLED) and is presented in pseudo-color or grayscale form, ultimately forming an infrared image visible to the human eye.

[0057] Furthermore, the optical lens 201 may include a lens and a lens barrel. The lens may utilize free-form surface technology to reduce spherical aberration, and aberrations may be corrected by combining multiple lenses. Lens materials may include germanium, zinc selenide, zinc sulfide, and silicon, which have high infrared transmittance and stability. The lens may include single-layer or multi-layer coatings, including spectroscopic coatings (to block non-infrared light) and anti-reflection coatings (to reduce specular reflection losses).

[0058] The lens barrel can be used to fix the position of the lens to prevent axial displacement of the lens. In addition, the lens barrel also contains an aperture to control the aperture of the infrared light beam entering the lens, affecting the depth of field and distortion. At the same time, the lens barrel also contains a filter to allow only specific infrared bands to pass through, thereby achieving selective capture of infrared bands.

[0059] According to a third aspect of the present disclosure, a method of using the infrared bioactivity meter is provided, the method comprising: Providing the above-mentioned constant heat radiation device 10; Adjusting the temperature of the heat radiation layer 2 of the constant heat radiation device 10 to be the same as the reference temperature; Place the object to be detected above the constant heat radiation device 10; The imaging element 20 acquires a thermal radiation image of the object to be detected.

[0060] For example, the object to be detected is human hand tissue. First, the constant thermal radiation device 10 is placed on a supporting structure such as a table, and then the thermal radiation amount of the constant thermal radiation device 10 is adjusted to be the same as the reference thermal radiation amount. The reference thermal radiation amount can be pre-set in the temperature controller 34. During this process, the temperature sensor 33 monitors the thermal radiation layer 2 and feeds back the signal to the temperature controller 34. The temperature controller 34 controls the conductive circuit 32 to energize to heat the carbon nanotubes, or to circulate the cooling medium into the cooling pipe to adjust the temperature of the thermal radiation layer 2, thereby adjusting the thermal radiation amount of the thermal radiation layer 2.

[0061] The person to be examined can then place the hand tissue above the constant heat radiation device 10, and can compress the proximal artery of the hand tissue using, for example, a mercury sphygmomanometer. The imaging element 20 can continuously capture images of the hand tissue to observe the thermal radiation data of the hand tissue. After no obvious changes in the image are observed, the arterial perfusion of the hand tissue is completely blocked, and then the pressure of the sphygmomanometer is quickly released. The image capture is continued to observe the thermal radiation of the hand tissue until the hand tissue is fully perfused. By comparing with the normal value, the tissue perfusion situation can be evaluated.

[0062] In addition, the target object to be detected can be an in vitro tissue, and the infrared bioactivity meter can be used to obtain a thermal image of the in vitro tissue to obtain thermal radiation data, so as to detect the difference in heat production capacity of metabolic activities and evaluate the activity of the in vitro tissue.

[0063] The preferred embodiments of the present disclosure are described in detail above in conjunction with the accompanying drawings. However, the present disclosure is not limited to the specific details of the above embodiments. Within the technical concept of the present disclosure, various simple modifications can be made to the technical solutions of the present disclosure, and these simple modifications all fall within the scope of protection of the present disclosure.

[0064] It should also be noted that the various specific technical features described in the above specific embodiments can be combined in any appropriate manner without contradiction. In order to avoid unnecessary repetition, the present disclosure will not further describe various possible combinations.

[0065] In addition, the various embodiments of the present disclosure may be arbitrarily combined, and as long as they do not violate the concept of the present disclosure, they should also be regarded as the contents disclosed by the present disclosure.

Claims

1. A constant heat radiation device, characterized in that: The heat-regulating layer comprises a temperature-regulating layer and a heat-radiating layer arranged above the temperature-regulating layer, wherein the temperature-regulating layer is used to regulate the temperature of the heat-radiating layer. The temperature-regulating layer comprises a plurality of temperature-raising structures and a plurality of temperature-cooling structures, and at least one temperature-raising structure is arranged adjacent to at least one temperature-cooling structure.

2. The constant heat radiation device according to claim 1, characterized in that: The thermal radiation layer has the same emissivity as the object to be detected.

3. The constant heat radiation device according to claim 2, characterized in that: The multiple heating structures and the multiple cooling structures are arranged in rows and columns. Along the row direction and the column direction, at least one cooling structure is provided between two adjacent heating structures, or at least one heating structure is provided between two adjacent cooling structures.

4. The constant heat radiation device according to claim 3, characterized in that: The temperature adjustment layer further includes a heat conducting structure, which is arranged between the temperature increasing structure and the temperature decreasing structure for heat conduction.

5. The constant heat radiation device according to claim 4, characterized in that: The heating structure includes carbon nanotubes suitable for electric current heating, and the cooling structure includes cooling pipes suitable for circulating cooling medium. wherein the carbon nanotubes are treated by plasma; and / or A protective layer is provided on the carbon nanotubes.

6. The constant heat radiation device according to claim 5, characterized in that: It also includes a temperature control layer arranged below the temperature adjustment layer, the temperature control layer includes a base member, and a conductive circuit, a temperature sensor and a temperature controller are provided on the base member. The conductive circuit is suitable for connecting the carbon nanotubes, the temperature sensor is suitable for monitoring the temperature of the heat radiation layer, and the temperature controller signal is connected to the temperature sensor and is used to control the on and off of the conductive circuit.

7. The constant heat radiation device according to claim 6, characterized in that: It also includes a heat insulation layer, which is arranged on the side of the temperature control layer away from the temperature adjustment layer, or The heat insulation layer is arranged on a side of the temperature control layer away from the temperature adjustment layer, and on each circumferential side of the temperature control layer and the temperature adjustment layer.

8. An infrared bioactivity measuring instrument, characterized in that: Suitable for detecting an object to be detected, comprising the constant heat radiation device according to any one of claims 1 to 7 and an imaging element arranged opposite to the constant heat radiation device, wherein the imaging element is used to detect the object to be detected between the imaging element and the constant heat radiation device.

9. The infrared bioactivity measuring instrument according to claim 8, characterized in that: The constant heat radiation devices and the imaging elements are arranged in multiple groups and are arranged around the target object to be detected. The imaging element is connected to a constant heat radiation device arranged opposite to the constant heat radiation device in the same group.

10. The infrared bioactivity measuring instrument according to claim 8, characterized in that: The imaging element can selectively capture near infrared light, mid infrared light, or far infrared light.

11. The infrared bioactivity measuring instrument according to claim 8, characterized in that: The imaging component includes an optical lens and a plurality of infrared detectors arranged in an array.

12. A method for using an infrared bioactivity meter, characterized in that: The infrared bioactivity meter according to any one of claims 8 to 11, wherein the method of use comprises: Providing a constant heat radiation device according to any one of claims 1 to 7; adjusting the heat radiation amount of the heat radiation layer of the constant heat radiation device to be the same as the reference heat radiation amount; placing the object to be detected above the constant heat radiation device; A thermal radiation image of the target object to be detected is obtained through the imaging element.

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