Tumor thermal therapy depth measuring and calculating method and device based on outdoor thermal environment

Abstract

The invention discloses a tumor thermal therapy depth measuring and calculating method and device based on an outdoor thermal environment, and the method comprises the steps: obtaining the skin surface temperature and the core temperature, and respectively presetting the boundary conditions of the skin surface temperature and the core temperature; a human tissue biological heat transfer model is constructed based on human tissue heat conduction, blood perfusion convection and conversion effects and metabolic heat production; analyzing and solving the human tissue biological heat transfer model to obtain a temperature distribution formula of the human tissue biological heat transfer model; and finally, taking the preset effective thermal therapy temperature threshold as the input of a temperature distribution formula of a human tissue biological heat transfer model, thereby obtaining the measurement and calculation results of the thermal therapy depth in different outdoor thermal environments. According to the method, the effective depth of human body superficial tumor thermal therapy in different outdoor thermal environments is calculated by constructing the human body tissue biological heat transfer model and carrying out analytical solution, so that a thermal therapy rehabilitation scheme is optimized, and the treatment effect of thermal therapy is improved.

Description

Technical Field

[0001] The present invention relates to the field of human body thermology, and in particular to a method and device for measuring the depth of tumor hyperthermia based on an outdoor thermal environment. Background Art

[0002] Malignant tumors are one of the leading causes of death worldwide, and their treatment has long been a focus of medical research. Traditional treatments include surgery, radiotherapy, chemotherapy, and immunotherapy, but these methods often have limitations, such as incomplete treatment, high recurrence rates, and significant side effects. Therefore, finding new treatments is crucial for improving cure rates and patients' quality of life. Tumor hyperthermia therapy utilizes external physical energy to stimulate thermal effects in biological tissues, heating the tumor to a temperature above its tolerance and maintaining it for a period of time to kill cancer cells. Hyperthermia is based on the principle that tumor cells are more sensitive to heat than normal cells. Heating can damage or kill tumor cells while minimizing the effects on normal cells. Clinically, hyperthermia can be categorized into local, regional, and whole-body based on the scope of action. Regional or whole-body hyperthermia involves a wider area and may cause adverse cardiac and hematologic reactions. Local hyperthermia, however, targets the tumor with minimal effects on surrounding normal tissue and is currently more commonly used. Basic research and clinical practice have confirmed that hyperthermia, while inactivating or even denaturing proteins and directly killing tumor cells, can also increase blood flow and oxygen supply, enhance sensitivity to other treatments, and modulate immunity through multiple pathways, stimulating anti-tumor immune responses. As a proven and effective tumor treatment, hyperthermia is gaining increasing attention and recognition. Summary of the Invention

[0003] In response to the above-mentioned deficiencies in the existing technology, the present invention provides a method and device for measuring the depth of tumor hyperthermia based on an outdoor thermal environment. By constructing a human tissue bioheat transfer model and performing analytical solutions, the effective depth of hyperthermia for superficial tumors in the human body under different outdoor thermal environments is calculated, thereby helping to optimize the hyperthermia plan and improve the therapeutic effect of hyperthermia.

[0004] In order to solve the above technical problems, the present invention adopts the following technical solutions:

[0005] A method for measuring the depth of tumor hyperthermia based on an outdoor thermal environment comprises the following steps:

[0006] S1. Real-time monitoring of outdoor thermal environment parameters to obtain skin surface temperature T s and core temperature T b , and pre-set the skin surface temperature T s and core temperature T b Boundary conditions;

[0007] S2. Construct a bioheat transfer model of human tissue based on heat conduction in human tissue, convection exchange of blood perfusion, and metabolic heat production;

[0008] S3. Analytically solving the human tissue bioheat transfer model and using the preset boundary conditions as inputs of the human tissue bioheat transfer model to obtain a temperature distribution formula of the human tissue bioheat transfer model;

[0009] S4. According to a preset effective hyperthermia temperature threshold, the preset effective hyperthermia temperature threshold is used as an input of a temperature distribution formula of a human tissue bioheat transfer model, thereby obtaining measurement results of hyperthermia depths under different outdoor thermal environments.

[0010] As a preferred solution, in step S2, the expression of the human tissue bioheat transfer model is:

[0011]

[0012] Where r is the radial distance from the local tissue to the arm axis, C b is the specific heat capacity of blood at constant pressure, k m is the thermal conductivity of the tissue, T a is the arterial blood temperature, W b is the blood perfusion rate, Q m is metabolic heat production, T is local tissue temperature, T b is the core temperature, T s is the skin temperature.

[0013] As a preferred solution, the blood perfusion rate is calculated using the following formula:

[0014]

[0015] Where, T b is the core temperature, T s is the skin temperature.

[0016] As a preferred solution, in step S3, the temperature distribution formula of the human tissue bioheat transfer model is expressed as:

[0017]

[0018] Where T is the local tissue temperature, r is the radial distance from the local tissue to the arm axis, and B is a constant determined by the heat transfer term of the blood perfusion rate; C1 is when r = R and T = T s The constant value determined under the boundary conditions is r=r c And T = T b The constant value determined under the boundary conditions of , R is the preset radial distance from the skin surface to the arm axis, r cIt is the pre-set radial distance from the outer edge of the core tissue to the arm axis.

[0019] As a preferred solution, in step S4, the calculation formula for the measurement results of the hyperthermia depth under different outdoor thermal environments is:

[0020] d=Rr e ;

[0021] Where d is the radial distance from the skin surface to the lower limit of the local tissue temperature reaching the effective treatment temperature, r e It is the radial distance from the position where the tissue temperature reaches the lower limit of the effective treatment temperature to the arm axis.

[0022] Accordingly, the present invention further provides a device for measuring the depth of tumor hyperthermia therapy based on an outdoor thermal environment, which is used to implement the above-mentioned method for measuring the depth of tumor hyperthermia therapy based on an outdoor thermal environment, comprising:

[0023] Environmental parameter monitoring module, used to monitor outdoor thermal environment parameters in real time and obtain skin surface temperature T s and core temperature T b , and pre-set the skin surface temperature T s and core temperature T b Boundary conditions;

[0024] Bioheat transfer model construction module, used to build a human tissue bioheat transfer model based on human tissue heat conduction, blood perfusion convection and metabolic heat production;

[0025] a model solving module, configured to analytically solve the human tissue bioheat transfer model and use the preset boundary conditions as inputs of the human tissue bioheat transfer model, thereby obtaining a temperature distribution formula of the human tissue bioheat transfer model;

[0026] The hyperthermia depth calculation module is used to use the preset effective hyperthermia temperature threshold as the input of the temperature distribution formula of the human tissue bioheat transfer model according to the preset effective hyperthermia temperature threshold, thereby obtaining the measurement results of the hyperthermia depth under different outdoor thermal environments.

[0027] As a preferred solution, in the bioheat transfer model construction module, the expression of the human tissue bioheat transfer model is:

[0028]

[0029] Where r is the radial distance from the local tissue to the arm axis, C b is the specific heat capacity of blood at constant pressure, k m is the thermal conductivity of the tissue, T a is the arterial blood temperature, W b is the blood perfusion rate, Qm is metabolic heat production, T is local tissue temperature, T b is the core temperature, T s is the skin temperature.

[0030] As a preferred solution, the blood perfusion rate is calculated using the following formula:

[0031]

[0032] Where, T b is the core temperature, T s is the skin temperature.

[0033] As a preferred solution, in the model solving module, the temperature distribution formula of the human tissue bioheat transfer model is expressed as:

[0034]

[0035] Where T is the local tissue temperature, r is the radial distance from the local tissue to the arm axis, and B is a constant determined by the heat transfer term of the blood perfusion rate; C1 is when r = R and T = T s The constant value determined under the boundary conditions is r=r c And T = T b The constant value determined under the boundary conditions of , R is the preset radial distance from the skin surface to the arm axis, r c It is the pre-set radial distance from the outer edge of the core tissue to the arm axis.

[0036] As a preferred solution, in the hyperthermia depth calculation module, the calculation formula for the measurement results of hyperthermia depth under different outdoor thermal environments is:

[0037] d=Rr e ;

[0038] Where d is the radial distance from the skin surface to the lower limit of the local tissue temperature reaching the effective treatment temperature, r e It is the radial distance from the position where the tissue temperature reaches the lower limit of the effective treatment temperature to the arm axis.

[0039] Compared with the prior art, the present invention has the following technical effects:

[0040] The human tissue bioheat transfer model of the present invention takes into account the heat conduction of human tissue, the perfusion heat effect of blood, and metabolic heat production, so that the error between the local tissue temperature predicted by the model and the actual tissue test temperature is reduced, the temperature field accuracy is improved, blood perfusion and metabolic heat production are linked, the body temperature regulation process under environmental changes is simulated, and a dynamic response is achieved; at the same time, the high metabolism and high perfusion characteristics of the tumor area make its temperature in the model significantly higher than that of normal tissue, thereby assisting in targeted therapy, and solving the problems of traditional tissue bioheat transfer models that ignore blood heat dissipation, over-prediction of deep tissue temperature, and inability to reflect the dynamic regulation of temperature on blood flow.

[0041] The present invention can analytically solve the biological heat transfer model for a specific measurement object, using the skin surface temperature and the human core temperature as the first-type heat transfer boundary conditions, to obtain the temperature distribution results of the tissue below the human skin surface, thereby clarifying the different effective depths of thermal therapy corresponding to the natural heating of the skin under different outdoor thermal environments. BRIEF DESCRIPTION OF THE DRAWINGS

[0042] In order to make the purpose, technical solutions and advantages of the invention more clear, the present invention will be further described in detail below with reference to the accompanying drawings, in which:

[0043] Figure 1 This is a flow chart of a method for calculating the depth of tumor hyperthermia based on an outdoor thermal environment disclosed in the present invention;

[0044] Figure 2 This is a scatter plot of tissue temperature distribution when the skin surface temperature is 41.3°C in this embodiment. DETAILED DESCRIPTION

[0045] In order to make the purpose, technical solutions and advantages of the embodiments of the present invention clearer, the technical solutions in the embodiments of the present invention will be clearly and completely described below in conjunction with the drawings in the embodiments of the present invention. Obviously, the described embodiments are part of the embodiments of the present invention, not all of the embodiments. The components of the embodiments of the present invention generally described and shown in the drawings here can be arranged and designed in various different configurations. Therefore, the following detailed description of the embodiments of the present invention provided in the drawings is not intended to limit the scope of the invention claimed for protection, but only represents selected embodiments of the present invention. Based on the embodiments in the present invention, all other embodiments obtained by ordinary technicians in this field without making creative work are within the scope of protection of the present invention.

[0046] The present invention will be described in further detail below with reference to the accompanying drawings.

[0047] The basic principle of hyperthermia is to take advantage of the fact that tumor cells cannot tolerate high temperatures. Under the heating of the treatment equipment, the tumor cells are allowed to reach 39.5-45°C and maintained for a certain period of hyperthermia, thereby killing the tumor cells and achieving the therapeutic effect. Under the condition of natural temperature rise in the outdoor thermal environment, the human skin temperature can reach 39.5°C, which meets the conditions for hyperthermia, but the effective depth of hyperthermia cannot be determined under different outdoor thermal environments. Therefore, the present invention constructs a human tissue bioheat transfer model, analyzes and solves the temperature of subcutaneous tissue, and obtains the temperature distribution structure of tissues at different depths, clarifying the different effective depths of hyperthermia corresponding to the natural temperature rise of the skin under different outdoor thermal environments.

[0048] Specifically, the present invention proposes a method for measuring the depth of tumor hyperthermia based on an outdoor thermal environment. Figure 1 As shown, the method includes:

[0049] S1. Real-time monitoring of outdoor thermal environment parameters to obtain skin surface temperature T s and core temperature T b , and pre-set the skin surface temperature T s and core temperature T b Boundary conditions;

[0050] S2. Construct a bioheat transfer model of human tissue based on heat conduction in human tissue, convection exchange of blood perfusion, and metabolic heat production;

[0051] The expression of the human tissue bioheat transfer model is:

[0052]

[0053] Where r is the radial distance from the local tissue to the arm axis, C b is the specific heat capacity of blood at constant pressure, k m is the thermal conductivity of the tissue, T a is the arterial blood temperature, W b is the blood perfusion rate, Q m is metabolic heat production, T is local tissue temperature, T b is the core temperature, T s is the skin temperature.

[0054] The blood perfusion rate is calculated by the following formula:

[0055]

[0056] Where, T b is the core temperature, T s is the skin temperature.

[0057] S3. Analytically solving the human tissue bioheat transfer model and using the preset boundary conditions as inputs of the human tissue bioheat transfer model to obtain a temperature distribution formula of the human tissue bioheat transfer model;

[0058] The temperature distribution formula of the human tissue bioheat transfer model is expressed as:

[0059]

[0060] Where T is the local tissue temperature, r is the radial distance from the local tissue to the arm axis, and B is a constant determined by the heat transfer term of the blood perfusion rate; C1 is when r = R and T = T s The constant value determined under the boundary conditions is r=r c And T = T b The constant value determined under the boundary conditions of , R is the preset radial distance from the skin surface to the arm axis, r c It is the pre-set radial distance from the outer edge of the core tissue to the arm axis.

[0061] S4. According to a preset effective hyperthermia temperature threshold, the preset effective hyperthermia temperature threshold is used as an input of a temperature distribution formula of a human tissue bioheat transfer model, thereby obtaining measurement results of hyperthermia depths under different outdoor thermal environments.

[0062] The calculation formula for the measurement results of the hyperthermia depth under different outdoor thermal environments is:

[0063] d=Rr e ;

[0064] Where d is the radial distance from the skin surface to the lower limit of the local tissue temperature reaching the effective treatment temperature, r e It is the radial distance from the position where the tissue temperature reaches the lower limit of the effective treatment temperature to the axis.

[0065] Accordingly, the present invention further provides a device for calculating the depth of tumor hyperthermia therapy based on an outdoor thermal environment, for implementing the above-mentioned method for calculating the depth of tumor hyperthermia therapy based on an outdoor thermal environment. The device for calculating the depth of tumor hyperthermia therapy comprises:

[0066] Environmental parameter monitoring module, used to monitor outdoor thermal environment parameters in real time and obtain skin surface temperature T s and core temperature T b , and pre-set the skin surface temperature T s and core temperature T b Boundary conditions;

[0067] Bioheat transfer model construction module, used to build a human tissue bioheat transfer model based on human tissue heat conduction, blood perfusion convection and metabolic heat production;

[0068] a model solving module, configured to analytically solve the human tissue bioheat transfer model and use the preset boundary conditions as inputs of the human tissue bioheat transfer model, thereby obtaining a temperature distribution formula of the human tissue bioheat transfer model;

[0069] The hyperthermia depth calculation module is used to use the preset effective hyperthermia temperature threshold as the input of the temperature distribution formula of the human tissue bioheat transfer model according to the preset effective hyperthermia temperature threshold, thereby obtaining the measurement results of the hyperthermia depth under different outdoor thermal environments.

[0070] The human tissue bioheat transfer model of the present invention takes into account the heat conduction of human tissue, the perfusion heat effect of blood, and metabolic heat production, so that the error between the local tissue temperature predicted by the model and the actual tissue test temperature is reduced, the temperature field accuracy is improved, blood perfusion and metabolic heat production are linked, the body temperature regulation process under environmental changes is simulated, and a dynamic response is achieved; at the same time, the high metabolism and high perfusion characteristics of the tumor area make its temperature in the model significantly higher than that of normal tissue, thereby assisting in targeted therapy, and solving the problems of traditional tissue bioheat transfer models that ignore blood heat dissipation, over-prediction of deep tissue temperature, and inability to reflect the dynamic regulation of temperature on blood flow.

[0071] As can be seen, the present invention can analytically solve the biological heat transfer model for a specific measurement object, using skin surface temperature and human core temperature as the first-class heat transfer boundary conditions, thereby obtaining the temperature distribution of tissue below the human skin surface. The following describes in more detail the method and device for measuring the depth of tumor hyperthermia therapy based on an outdoor thermal environment, as proposed by the present invention, through specific examples.

[0072] In this embodiment, the human arm is used as the research object, and the heat transfer model of the human arm is simplified to a cylindrical steady-state heat transfer model. The cylindrical mathematical model takes the center of the arm as the axis, and the radius of the human arm is set to 0.04m in this embodiment. The response range of the arm to the ambient temperature is within 0.02m from the skin surface to the inside of the tissue, so the distance between the human tissue affected by the outdoor thermal environment temperature and the arm axis is 0.02m-0.04m. The mathematical model constructed in this embodiment mainly considers three heat transfer factors in human tissue: 1) heat conduction of human tissue; 2) convective heat transfer of blood perfusion; 3) metabolic heat production Q m , so the mathematical expression of the constructed human tissue heat transfer model is as follows:

[0073]

[0074] Where r is the radial distance from the local tissue to the arm axis; C b is the specific heat capacity of blood at constant pressure, where C b =4187.0J / (K·℃); k m is the thermal conductivity of the tissue, where k m =0.22W / (m·K); T a is the arterial blood temperature, where T a =37.0℃;W b is the blood perfusion rate; Q m is metabolic heat production, where Q m =400(W / m 3 ); T is the local tissue temperature; T b is the core temperature, T s is the skin temperature, where T b =37℃.

[0075] Through the above deformation, the temperature distribution formula of the human tissue bioheat transfer model can be expressed as:

[0076]

[0077] Where B is a constant determined by the heat transfer term of the blood perfusion rate; C1 is when r = r and T = T s The constant value determined under the boundary conditions is r=r c And T = T b The constant value determined under the boundary conditions of , R is the preset radial distance from the skin surface to the arm axis, r c It is the pre-set radial distance from the outer edge of the core tissue to the arm axis.

[0078] The blood perfusion rate is calculated by the following formula:

[0079]

[0080] Where, T b is the core temperature, T s is the skin temperature.

[0081] In this specific embodiment, the skin surface temperature T s =41.3℃, core temperature T b =37℃ is the boundary condition of the human tissue heat transfer model, that is, when the skin surface temperature T s =41.3℃, r=R=0.04m; core temperature T b =37℃, r=r c =0.02m.

[0082] Then W b=0.655(kg / m 3 ·s).

[0083] The data of the embodiment is substituted into the human tissue heat transfer model for analytical solution. The specific solution process is as follows:

[0084]

[0085] T-6700.39r 2 =C1lnr+C2

[0086] At this time, substitute the boundary condition: r = r c =0.02m, T=T s =37℃, that is:

[0087] 34.319844=-3.91C1+C2;

[0088] When r=R=0.04m, T=T b =41.3℃, that is:

[0089] 30.579376=-3.22C1+C2;

[0090] Then we can get C1=-5.42; C2=13.12.

[0091] Therefore, the temperature distribution formula of the model when the skin surface temperature is 41.3℃ and the core temperature is 37℃ is: T = 6700.39r 2 -5.42ln r+13.12.

[0092] After the solution of the model is expressed graphically, Figure 2 As shown by Figure 2 It can be analyzed that when T = 39.5 ° C, r = 0.035m, so 0.04-0.035 = 0.005m, which means the outdoor temperature is 29 ° C and the solar radiation is 810.5w / m 2 When the skin temperature is approximately 0.005m inward from the skin surface, the hyperthermia temperature requirement of 39.5°C (the lower limit of the effective treatment temperature) is met. Considering that tumor temperature is 1-3°C higher than normal tissue, the conservative range of approximately 0.009m inward from the skin surface meets the hyperthermia requirement.

[0093] In summary, the human tissue bioheat transfer model of this embodiment analytically solves the subcutaneous tissue temperature and obtains the temperature distribution of tissues at different depths. Considering that the effective treatment temperature range for tumors with hyperthermia is 39.5-45°C, and that tumor temperature is 1-3°C higher than normal tissue, the effective hyperthermia depth for superficial human tumors in different outdoor thermal environments can be calculated. Furthermore, the human tissue bioheat transfer model of this embodiment takes into account the thermal conduction of human tissue, the perfusion heat effect of blood, and metabolic heat production. This reduces the error between the model's predicted local tissue temperature and the actual tissue test temperature, improves temperature field accuracy, and links blood perfusion with metabolic heat production to simulate the body's temperature regulation process during environmental changes, achieving dynamic response. Furthermore, the high metabolic and high perfusion characteristics of the tumor region cause the model's temperature to be significantly higher than that of normal tissue, thereby assisting in targeted therapy. This addresses the issues of traditional tissue bioheat transfer models that ignore blood heat dissipation, overestimate deep tissue temperature predictions, and fail to reflect the dynamic regulation of blood flow by temperature.

[0094] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention and are not limiting. Although the present invention has been described with reference to the preferred embodiments of the present invention, it should be understood by those skilled in the art that various changes can be made in form and details without departing from the spirit and scope of the present invention as defined in the appended claims.

Claims

1. A method for measuring the depth of tumor hyperthermia based on an outdoor thermal environment, characterized in that: The steps include: S1. Real-time monitoring of outdoor thermal environment parameters to obtain skin surface temperature T s and core temperature T b , and pre-set the skin surface temperature T s and core temperature T b Boundary conditions; S2. Construct a bioheat transfer model of human tissue based on heat conduction in human tissue, convection exchange of blood perfusion, and metabolic heat production; S3. Analytically solving the human tissue bioheat transfer model and using the preset boundary conditions as inputs of the human tissue bioheat transfer model to obtain a temperature distribution formula of the human tissue bioheat transfer model; S4. According to a preset effective hyperthermia temperature threshold, the preset effective hyperthermia temperature threshold is used as an input of a temperature distribution formula of a human tissue bioheat transfer model, thereby obtaining measurement results of hyperthermia depths under different outdoor thermal environments.

2. The method for calculating the depth of tumor hyperthermia based on an outdoor thermal environment according to claim 1, characterized in that: In step S2, the expression of the human tissue bioheat transfer model is: Where r is the radial distance from the local tissue to the arm axis, C b is the specific heat capacity of blood at constant pressure, k m is the thermal conductivity of the tissue, T a is the arterial blood temperature, W b is the blood perfusion rate, Q m is metabolic heat production, T is local tissue temperature, T b is the core temperature, T s is the skin temperature.

3. The method for calculating the depth of tumor hyperthermia based on an outdoor thermal environment according to claim 2, characterized in that: The blood perfusion rate is calculated by the following formula: Where, T b is the core temperature, T s is the skin temperature.

4. The method for calculating the depth of tumor hyperthermia based on an outdoor thermal environment according to claim 1, wherein: In step S3, the temperature distribution formula of the human tissue bioheat transfer model is expressed as: Where T is the local tissue temperature, r is the radial distance from the local tissue to the arm axis, and B is a constant determined by the heat transfer term of the blood perfusion rate; C1 is when r = R and T = T s The constant value determined under the boundary conditions is r=r c And T = T b The constant value determined under the boundary conditions of , R is the preset radial distance from the skin surface to the arm axis, r c It is the pre-set radial distance from the outer edge of the core tissue to the arm axis.

5. The method for calculating the depth of tumor hyperthermia based on an outdoor thermal environment according to claim 4, characterized in that: In step S4, the calculation formula for the measurement results of the hyperthermia depth under different outdoor thermal environments is: d=R-r e ; Where d is the radial distance from the skin surface to the lower limit of the local tissue temperature reaching the effective treatment temperature, r e The radial distance from the position where the tissue temperature reaches the lower limit of the effective treatment temperature to the arm axis.

6. A device for calculating the depth of tumor hyperthermia based on an outdoor thermal environment, used to implement the method for calculating the depth of tumor hyperthermia based on an outdoor thermal environment as claimed in claim 1, characterized in that: include: ； Environmental parameter monitoring module, used to monitor outdoor thermal environment parameters in real time and obtain skin surface temperature T s and core temperature T b , and pre-set the skin surface temperature T s and core temperature T b Boundary conditions; Bioheat transfer model construction module, used to build a human tissue bioheat transfer model based on human tissue heat conduction, blood perfusion convection and metabolic heat production; a model solving module, configured to analytically solve the human tissue bioheat transfer model and use the preset boundary conditions as inputs of the human tissue bioheat transfer model, thereby obtaining a temperature distribution formula of the human tissue bioheat transfer model; The hyperthermia depth calculation module is used to use the preset effective hyperthermia temperature threshold as the input of the temperature distribution formula of the human tissue bioheat transfer model according to the preset effective hyperthermia temperature threshold, thereby obtaining the measurement results of the hyperthermia depth under different outdoor thermal environments.

7. The device for measuring tumor hyperthermia depth based on outdoor thermal environment according to claim 6, characterized in that: In the bioheat transfer model construction module, the expression of the human tissue bioheat transfer model is: Where r is the radial distance from the local tissue to the arm axis, C b is the specific heat capacity of blood at constant pressure, k m is the thermal conductivity of the tissue, T a is the arterial blood temperature, W b is the blood perfusion rate, Q m is metabolic heat production, T is local tissue temperature, T b is the core temperature, T s is the skin temperature.

8. The device for measuring tumor hyperthermia depth based on outdoor thermal environment according to claim 7, characterized in that: The blood perfusion rate is calculated by the following formula: Where, T b is the core temperature, T s is the skin temperature.

9. The device for measuring tumor hyperthermia depth based on outdoor thermal environment according to claim 6, characterized in that: In the model solving module, the temperature distribution formula of the human tissue bioheat transfer model is expressed as: Where T is the local tissue temperature, r is the radial distance from the local tissue to the arm axis, and B is a constant determined by the heat transfer term of the blood perfusion rate; C1 is when r = R and T = T s The constant value determined under the boundary conditions is r=r c And T = T b The constant value determined under the boundary conditions of , R is the preset radial distance from the skin surface to the arm axis, r c It is the pre-set radial distance from the outer edge of the core tissue to the arm axis.

10. The device for measuring tumor hyperthermia depth based on outdoor thermal environment according to claim 9, characterized in that: In the hyperthermia depth calculation module, the calculation formula for the measurement results of hyperthermia depth under different outdoor thermal environments is: d=R-r e ; Where d is the radial distance from the skin surface to the lower limit of the local tissue temperature reaching the effective treatment temperature, r e It is the radial distance from the position where the tissue temperature reaches the lower limit of the effective treatment temperature to the arm axis.

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