Measurement device, measurement method and control program

Abstract

To provide a measurement device, measurement method and control program capable of simultaneously measuring multiple kinds of test contents for a test subject.SOLUTION: A measurement device according to the present disclosure comprises: a heat insulating material; a first temperature sensor provided on a bottom surface of the heat insulating material; a second temperature sensor provided on an upper surface of the heat insulating material; a first electrical conductor having a contact surface with a test subject, and arranged so as to cover at least a part of a side surface of the heat insulating material; a second electrical conductor having a contact surface with the test subject, and arranged so as to cover at least another part of the side surface of the heat insulating material and electrically separated from the first electrical conductor; a first arithmetic processing unit that calculates the core body temperature of the test subject based on detection result of the first and second temperature sensors; and a second arithmetic processing unit that calculates the cardiac potential of the test subject based on electrical signals obtained from the first and second electrical conductors.SELECTED DRAWING: Figure 1

Description

[Technical Field]

[0001] The present disclosure relates to a measurement device, a measurement method, and a control program. [Background technology]

[0002] In recent years, global warming has led to frequent extreme weather events and natural disasters, threatening our daily lives. In particular, preventing heatstroke, which is on the rise due to extreme summer heat, has become an urgent social issue. Heatstroke occurs when prolonged exposure to high temperatures and humidity disrupts the thermoregulatory system, resulting in internal heat buildup. Because heatstroke develops through a rise in the body's internal temperature (core temperature), maintaining core temperature below 38°C (38.5°C during heat acclimation) is recommended as a preventative measure. Therefore, there is a need for a technology that can easily and accurately measure core temperature in everyday life. Core temperature measurement typically involves inserting a thermometer directly into a body cavity, making it highly invasive and difficult to use in everyday life. Meanwhile, a method for estimating core temperature from heat flow at the skin surface has been developed in recent years, and research into wearable sensors based on this method is progressing, but measurement accuracy remains an issue. As a solution to such a problem, Patent Document 1 discloses a technology for estimating core body temperature with high accuracy. [Prior art documents] [Patent documents]

[0003] [Patent Document 1] Patent No. 7424495 Summary of the Invention [Problem to be solved by the invention]

[0004] In recent years, there has been a demand for not only estimating the core body temperature of a living subject, but also for testing multiple types of test contents in parallel.

[0005] An object of the present disclosure is to provide a measurement device, a measurement method, and a control program that solve the above-mentioned problems. [Means for solving the problem]

[0006] The measuring device according to the present disclosure comprises: a first temperature sensor provided on the bottom surface of the insulating material, which is the contact surface between the insulating material and the living body being tested; a second temperature sensor provided on the top surface of the insulating material, which is the surface opposite the bottom surface of the insulating material; a first electrical conductor having a contact surface with the test subject and arranged to cover at least a portion of the side surface of the insulating material; a second electrical conductor having a contact surface with the test subject and arranged to cover at least another portion of the side surface of the insulating material and electrically separated from the first electrical conductor; a first calculation processing unit that calculates the core body temperature of the test subject based on the detection results of the first temperature sensor and the second temperature sensor; and a second calculation processing unit that calculates the cardiac potential of the test subject based on the electrical signals obtained from the first electrical conductor and the second electrical conductor.

[0007] The measurement method disclosed herein is a measurement method using a multimodal sensor comprising: a first temperature sensor provided on the bottom surface of the insulating material, which is the contact surface between the insulating material and the living body being tested; a second temperature sensor provided on the top surface of the insulating material, which is the surface opposite the bottom surface of the insulating material; a first electrical conductor having a contact surface with the test subject and arranged to cover at least a portion of the side surface of the insulating material; and a second electrical conductor having a contact surface with the test subject and arranged to cover at least another portion of the side surface of the insulating material and to be electrically separated from the first electrical conductor, wherein the deep body temperature of the test subject is calculated based on the detection results of the first temperature sensor and the second temperature sensor, and the cardiac potential of the test subject is calculated based on the electrical signals obtained from the first electrical conductor and the second electrical conductor,

[0008] The control program of the present disclosure is a control program that causes a computer to execute a measurement process using a multimodal sensor that includes a first temperature sensor provided on the bottom surface of the insulating material, which is the contact surface between the insulating material and the living body being tested, a second temperature sensor provided on the top surface of the insulating material, which is the surface opposite the bottom surface of the insulating material, a first electrical conductor that has a contact surface with the test subject and is arranged to cover at least a portion of the side surface of the insulating material, and a second electrical conductor that has a contact surface with the test subject and is arranged to cover at least another portion of the side surface of the insulating material and is electrically separated from the first electrical conductor, and causes the computer to execute a process of calculating the core body temperature of the test subject based on the detection results of the first temperature sensor and the second temperature sensor, and a process of calculating the cardiac potential of the test subject based on the electrical signals obtained from the first electrical conductor and the second electrical conductor. [Effects of the Invention]

[0009] The present disclosure can provide a measurement device, a measurement method, and a control program that can simultaneously measure multiple types of inspection content on an inspection object. [Brief explanation of the drawings]

[0010] [Figure 1] FIG. 1 is a diagram illustrating an example of the configuration of a measurement device according to the present disclosure. [Figure 2] 1 is a schematic perspective view showing the appearance of a probe provided in a measurement device according to the present disclosure. [Figure 3] FIG. 3 is a schematic cross-sectional view of a probe provided in a measurement device of a first comparative example. [Figure 4] FIG. 10 is a schematic cross-sectional view of a probe provided in a measurement device of a second comparative example. [Figure 5] FIG. 10 is a diagram showing a two-dimensional axisymmetric model of a probe provided in a measurement device of a second comparative example and its surrounding environment. [Figure 6] FIG. 10 is a diagram showing the relationship between the thermal conductivity of each of the probe body and the probe cover and the error in the estimated value of the core body temperature in the measurement device of the second comparative example. [Figure 7] (a) A diagram showing the relationship between the air temperature and wind speed and the error in the estimated value of the core body temperature in the measurement device of the first comparative example. (b) A diagram showing the relationship between the air temperature and wind speed and the error in the estimated value of the core body temperature in the measurement device of the second comparative example. [Figure 8] FIG. 10 is a diagram for explaining a heat loss rate. [Figure 9] (a) A diagram showing the calculation results of the heat loss rate under a first wind speed condition in the measurement device of the first comparative example. (b) A diagram showing the calculation results of the heat loss rate under a second wind speed condition in the measurement device of the first comparative example. (c) A diagram showing the calculation results of the heat loss rate under a first wind speed condition in the measurement device of the second comparative example. (d) A diagram showing the calculation results of the heat loss rate under a second wind speed condition in the measurement device of the second comparative example. [Figure 10] (a) A diagram showing the relationship between the thickness of the probe cover and the error in the estimated value of core body temperature in the measurement device of the second comparative example. (b) A diagram showing the relationship between the diameter and thickness of the probe body and the error in the estimated value of core body temperature in the measurement device of the second comparative example. [Figure 11] 10A and 10B are diagrams showing changes in air temperature and wind speed over time during measurements using measuring devices of the respective comparative examples. [Figure 12] 12A and 12B are diagrams showing the change over time in error of the estimated value of the core body temperature measured by the measuring devices of the respective comparative examples when the air temperature and wind speed are changed suddenly under the conditions shown in FIG. 11. [Figure 13] 10A and 10B are diagrams showing the time changes of the time derivatives of the skin temperature and the sensor temperature measured by the measuring devices of the respective comparative examples. [Figure 14] 10A and 10B are diagrams showing examples of spatial distribution of the magnitude of the time derivative value of temperature in a probe provided in each of the measurement devices of the comparative examples. [Figure 15](a) A diagram showing the appearance of a prototype of a probe provided in a measurement device of a second comparative example. (b) A diagram showing the time change in wind speed during measurement using the prototype. (c) A diagram showing the time change in the estimated and reference values ​​of core body temperature measured using the prototype. (d) A diagram showing Bland-Altman plots of the estimated and reference values ​​of core body temperature measured using the prototype. [Figure 16] 1 is a schematic cross-sectional view of a probe provided in a measurement device according to the present disclosure. [Figure 17] 10A and 10B are diagrams for explaining a method for measuring core body temperature using a measurement device according to the present disclosure. [Figure 18] 10 is a schematic cross-sectional view showing a modified example of a probe provided in a measurement device according to the present disclosure. FIG. [Figure 19] FIG. 18 is a diagram showing errors in estimated values ​​of core body temperature when modified versions of the probes shown in FIG. 17 are used. [Figure 20] 10 is a diagram showing changes over time in the estimated value of core body temperature measured by the measurement device according to the present disclosure and the actual measured value of core body temperature (rectal temperature). FIG. [Figure 21] 10A and 10B are diagrams showing changes over time in cardiac potential measured by a measurement device according to the present disclosure. [Figure 22] 10 is a diagram showing changes over time in the estimated value of the amount of sweat measured by the measurement device according to the present disclosure and the actual measured value of the amount of sweat. FIG. [Figure 23] FIG. 2 is a block diagram illustrating an example of a hardware configuration that realizes a measurement function of a measurement device according to the present disclosure. DETAILED DESCRIPTION OF THE INVENTION

[0011] Hereinafter, embodiments will be described with reference to the drawings. Note that the drawings are simplified, and the technical scope of the embodiments should not be narrowly interpreted based on the description in the drawings. Furthermore, identical elements are given the same reference numerals, and duplicate explanations will be omitted.

[0012] In the following embodiments, when necessary for convenience, the description will be divided into multiple sections or embodiments. However, unless otherwise specified, they are not unrelated to each other, and one is a partial or complete modification, application example, detailed explanation, supplementary explanation, etc. of the other. Furthermore, in the following embodiments, when the number of elements (including the number, numerical value, amount, range, etc.) is mentioned, it is not limited to that specific number, and may be more or less than the specific number, unless otherwise specified or when it is clearly limited to a specific number in principle.

[0013] Furthermore, in the following embodiments, the components (including operational steps, etc.) are not necessarily essential unless otherwise specified or considered to be clearly essential in principle. Similarly, in the following embodiments, when referring to the shape, positional relationship, etc. of components, etc., it is intended to include those that are substantially similar or approximate to the shape, etc., unless otherwise specified or considered to be clearly not essential in principle. The same applies to the above numbers, etc. (including numbers, numerical values, amounts, ranges, etc.).

[0014] <First Embodiment> FIG. 1 is a diagram illustrating an example of the configuration of a measurement device 1 according to a first embodiment. As illustrated in FIG. 1, the measurement device 1 includes a probe (sensor probe) 10 and an arithmetic processing circuit 20. The measurement device 1 is also called a multimodal sensor. FIG. 1 illustrates a schematic cross-sectional view of the probe 10. FIG. 2 is a schematic perspective view illustrating the appearance of the probe 10.

[0015] The probe 10 is configured to be attachable to and detachable from a living body (mainly a human body) that is an object to be examined TG. The probe 10 includes a probe main body 11 and a probe cover 12.

[0016] The probe body 11 includes a heat insulating material 111, a temperature sensor (first temperature sensor) 112, and a temperature sensor (second temperature sensor) 113.

[0017] The heat insulating material 111 defines the outer shape of the probe main body 11. Here, since the heat insulating material 111 has a cylindrical shape, the probe main body 11 also has a cylindrical shape. However, the heat insulating material 111 is not limited to a cylindrical shape, and may have a prismatic or polygonal prismatic shape. The heat insulating material 111 is made of, for example, PDMS (dimethylpolysiloxane).

[0018] The temperature sensor 112 is provided on the bottom surface of the heat insulating material 111, which is the surface that comes into contact with the test subject TG. When the probe 10 is attached to the test subject TG, the temperature sensor 112 detects the skin temperature Tskin of the test subject TG.

[0019] The temperature sensor 113 is provided on the top surface of the heat insulating material 111, which is the surface opposite to the bottom surface of the heat insulating material 111. The temperature sensor 113 detects the temperature Tsen of the top surface of the heat insulating material 111.

[0020] The probe cover 12 is provided so as to cover the area of ​​the probe main body 11 other than the surface that comes into contact with the test object TG. In other words, the probe cover 12 is provided so as to cover the side and top surfaces of the probe main body 11 (thermal insulating material 111).

[0021] Specifically, the probe cover 12 has an electric conductor (first electric conductor) 121, an electric conductor (second electric conductor) 122, and an insulator 123.

[0022] The electrical conductor 121 has a contact surface at its end with the test object TG, and is provided so as to cover at least a portion of the side surface of the heat insulating material 111. The electrical conductor 122 has a contact surface at its end with the test object TG, and is provided so as to cover at least another portion of the side surface of the heat insulating material 111. The electrical conductors 121 and 122 are provided so as to be electrically separated from each other. The electrical conductors 121 and 122 are made of a material having high electrical conductivity and high thermal conductivity (a material having at least a higher thermal conductivity than the heat insulating material 111). For example, the electrical conductors 121 and 122 are made of Al, Cu, or an alloy containing either Al or Cu.

[0023] The insulator 123 is provided between the electrical conductors 121 and 122 and serves as a probe cover together with the electrical conductors 121 and 122 to cover the side and top surfaces of the probe body 11 (thermal insulating material 111). The insulator 123 is made of a material with low electrical conductivity and high thermal conductivity (a material with at least higher thermal conductivity than the thermal insulating material 111). For example, the insulator 123 is made of either AlN or SiC.

[0024] The insulator 123 also serves to connect and fix the electrical conductors 121 and 122. However, if the electrical conductors 121 and 122 can be fixed without the insulator 123, the insulator 123 may not be provided. In that case, the probe cover 12 is formed by the electrical conductors 121 and 122.

[0025] The arithmetic processing circuit 20 executes predetermined arithmetic processing on the detection results from the probe 10, thereby calculating measurement results for a plurality of types of test contents of the test object TG.

[0026] The arithmetic processing circuit 20 has a first arithmetic processing unit 201, a second arithmetic processing unit 202, and a third arithmetic processing unit 203. The first arithmetic processing unit 201 calculates an estimated value of the deep body temperature of the test subject TG based on the detection results of each of the temperature sensors 112 and 113. The second arithmetic processing unit 202 calculates an estimated value of the cardiac potential of the test subject TG based on the electrical signals obtained from each of the electrical conductors 121 and 122. The third arithmetic processing unit 203 calculates an estimated value of the amount of sweating of the test subject TG based on the detection result of the temperature sensor 112 and the calculation result (estimated value of the deep body temperature) by the first arithmetic processing unit 201.

[0027] <How to measure core body temperature> Before describing the method for measuring the core body temperature of the test subject TG using the measurement device 1, the present inventors will explain the details of their preliminary investigations.

[0028] FIG. 3 is a schematic cross-sectional view of a probe 50 provided in a previously studied measurement device 5. Since the measurement device 5 is a device to be compared with the measurement device 1 according to the present disclosure, it is also referred to as a measurement device of a first comparative example. However, the contents described regarding the measurement device 5 may be adopted as part of the present invention. Note that FIG. 3 also shows a thermal equivalent circuit of the probe 50 and its surrounding environment. FIG. 3 also shows a part (skin) of a human body that is the test subject TG. The skin of the test subject TG has a skin 101 and a deep part (core) 102 inside the skin 101.

[0029] Unlike the probe 10 provided in the measuring device 1, the probe (sensor probe) 50 provided in the measuring device 5 does not have a probe cover 12. That is, in the measuring device 5, the probe 50 is configured by only the probe body 11.

[0030] The measurement device 5 has a measurement probe 50 made of a heat insulating material 111 equipped with temperature sensors 112, 113 capable of measuring the skin temperature and the temperature of its opposing surface, and when the probe 50 is brought into contact with the skin 101 of the test subject TG, the deep body temperature of the test subject TG is estimated from the temperatures detected by the temperature sensors 112, 113. Specifically, assuming that there is a steady one-dimensional temperature distribution in the vicinity of the sensor probe 50, the deep body temperature Tbody is estimated from the skin temperature Tskin measured by the temperature sensors 112, 113 and the temperature Tsen of its opposing surface, as shown in equation (1).

[0031]

number

[0032] Here, Rskin and Rsen represent the thermal resistance of the skin 101 and the sensor probe 50, respectively. The horizontal (y-axis) heat flow in the skin 101, which is not taken into account in this method, fluctuates due to changes in the air temperature (Tair) and air currents that occur in daily life, and this is a factor that causes errors in measuring the core body temperature Tbody. To solve this problem, the inventor next considered measurement device 6.

[0033] FIG. 4 is a schematic cross-sectional view of a probe 60 provided in a previously studied measurement device 6. Since the measurement device 6 is a device to be compared with the measurement device 1 according to the present disclosure, it is also referred to as a measurement device of a second comparative example. However, the contents described regarding the measurement device 6 may also be adopted as part of the present invention. Note that, as in FIG. 3, FIG. 4 also shows a part of the human body (skin) that is the test target TG.

[0034] The probe (sensor probe) 60 provided in the measuring device 6 further includes a probe cover 62 compared to the probe 50 provided in the measuring device 5. That is, in the measuring device 6, the probe 60 is composed of the probe body 11 and the probe cover 62.

[0035] The probe cover 62 is provided to cover the area of ​​the probe main body 11 other than the surface that comes into contact with the test object TG. In other words, the probe cover 62 is provided to cover the side and top surfaces of the probe main body 11 (thermal insulating material 111). The probe cover 62 is made of a material that has high electrical conductivity and high thermal conductivity (a material that has at least a higher thermal conductivity than the thermal insulating material 111). For example, the probe cover 62 is made of an electrical conductor such as Al, Cu, or an alloy containing either Al or Cu.

[0036] As a result, measurement device 6 can control the horizontal (y-axis) heat flow in skin 101 without being affected by the thermophysical properties of air (Rair), which change due to temperature and airflow, which was one of the factors causing measurement errors in measurement device 5. Furthermore, measurement device 6 uses a calculation model for deep body temperature Tbody that takes into account the heat capacity Cskin of skin 101 when estimating the deep body temperature in order to compensate for changes in heat flow during unsteady conditions, in addition to the horizontal (y-axis) heat flow in skin 101, thereby estimating deep body temperature Tbody from skin temperature Tskin and sensor temperature Tsen measured by sensor probe 60, as shown in equation (2). Here, Rleak represents the thermal resistance of the horizontal heat flow in skin 101.

[0037]

number

[0038] Numerical analysis using the finite element method was performed to conduct a basic study on the method of measuring core body temperature using the measurement device 6. The steady-state and unsteady-state temperature distributions in the probe 60 and its surrounding environment, which consist of the probe body 11, the probe cover 62, the biological tissue of the TG under test, and the air, were determined by calculating equations (3), (4), and (5) for the heat transport between each material and the air flow.

[0039]

number

number

number

[0040] Here, k, Cp, ρ, T, u, μ, p, and t represent the thermal conductivity, heat capacity, density, temperature, velocity (fluid only), viscosity (fluid only), pressure (fluid only), and time of the material, respectively. tr represents the transpose matrix. The calculations were performed using the finite element analysis software COMSOL Multiphysics (registered trademark). The calculation model used was a two-dimensional axisymmetric model consisting of a cylindrical probe body, probe cover, the skin of the test subject TG, and air, as shown in Figure 5. The boundary conditions were: ambient temperature Tair and wind speed Vin on the upper surface of the air, an outflow boundary on the air side, core body temperature Tbody on the lower surface of the skin, and an adiabatic boundary on the skin side. The calculations were performed under a no-slip condition at the interface between the probe cover and air. In Figure 5, rsen represents the radius of the probe body 11, tsen represents the thickness of the probe body 11, tcover1 represents the thickness of the portion of the probe cover 62 arranged along the side of the probe body 11, and tcover2 represents the thickness of the portion of the probe cover 62 arranged along the top surface of the probe body 11.

[0041] Fig. 6 is a diagram showing the relationship between the thermal conductivity of each of the probe body 11 and the probe cover 62 in the measurement device 6 and the error in the estimated value (calculation result) of the steady-state core body temperature. In Fig. 6, the horizontal axis represents the thermal conductivity of the probe body 11, and the vertical axis represents the thermal conductivity of the probe cover 62. Note that this calculation was performed under the conditions of Tair = 20 [°C], Tbody = 37 [°C], Vin = 5 [m / s], rsen = 15 [mm], tsen = 5 [mm], tcover1 = 5 [mm], and tcover2 = 5 [mm].

[0042] First, it was confirmed that there is an optimum value for the thermal conductivity of the probe body 11 to reduce the estimation error of the core body temperature, as shown in Fig. 6. This is thought to be because the lower the thermal conductivity of the probe body 11, the greater the unaccounted heat flow between the skin and the air, which is one of the factors that contribute to the estimation error of the core body temperature, and the higher the thermal conductivity of the probe body 11, the greater the heat flow from the skin away from the probe body 11 to the probe body 11, which is another factor that contributes to the estimation error of the core body temperature.

[0043] 6, it was confirmed that the higher the thermal conductivity of the probe cover 62, the smaller the estimation error of the core body temperature. This is thought to be because the higher the thermal conductivity of the probe cover 62, the smaller the unaccounted heat flow between the skin and the air, which is one of the factors that causes estimation error of the core body temperature.

[0044] From the calculation results of FIG. 6, it is preferable that the probe body 11 be made of a material with a thermal conductivity of approximately 2 [W / (m·K)]. However, materials with a thermal conductivity of approximately 2 [W / (m·K)] are brittle materials that are difficult to process, such as glass or ceramic. Therefore, the probe body 11 may be made of polydimethylsiloxane (PDMS), which has a relatively high thermal conductivity among materials with excellent moldability, although its thermal conductivity is inferior to that of glass or ceramic. The thermal conductivity of PDMS is 0.27 [W / (m·K)]. In the following, the probe body 11 is described as being made of PDMS. In contrast, the probe cover 62 is preferably made of aluminum or other materials with a relatively high thermal conductivity in order to reduce costs. The thermal conductivity of aluminum is 237 [W / (m·K)]. In the following, the probe cover 62 is described as being made of aluminum.

[0045] Figure 7 shows the relationship between the air temperature and wind speed and the error in the estimated value of core body temperature for each of the measuring devices 5 and 6. Figure 7(a) shows the relationship between the air temperature and wind speed and the error in the estimated value of core body temperature at steady state for the measuring device 5, and Figure 7(b) shows the relationship between the air temperature and wind speed and the error in the estimated value of core body temperature for the measuring device 6. In Figure 7, the horizontal axis represents wind speed Vair, and the vertical axis represents air temperature Tair. Note that this calculation was performed under the conditions of Tbody = 37°C, rsen = 15 mm, tsen = 5 mm, tcover1 = 5 mm, and tcover2 = 5 mm.

[0046] From the calculation results in Figure 7, it was confirmed that the measurement device 6 with probe 60 can estimate the core body temperature Tbody more accurately over a wider temperature range and wider wind speed range than the measurement device 5 with probe 50. In addition, it was confirmed that a common feature of the measurement devices 5 and 6 is that the lower the air temperature or the higher the wind speed, the larger the core body temperature estimation error tends to be. This is thought to be because the lower the air temperature, the greater the difference between the core body temperature and the air temperature, and the higher the wind speed, the greater the thermal conductivity of the air, which increases the unaccounted heat flow that moves directly from the skin to the air.

[0047] Here, to analyze the horizontal heat flow of the skin, which is one of the error factors common to measurement devices 5 and 6, the ratio of the “normal heat flux in Area II” to the “total heat flux in Area I and Area II” in the measurement region shown in Figure 8 is defined as the heat loss rate [%].

[0048] FIG. 9 is a diagram showing the calculation results of the heat loss rate in each of the measuring devices 5 and 6.

[0049] FIG. 9(a) shows the calculation results of the heat loss rate under the conditions of Tair=20°C and Vair=0 m / s using the measurement device 5. FIG. 9(b) shows the calculation results of the heat loss rate under the conditions of Tair=20°C and Vair=5 m / s using the measurement device 5. FIG. 9(c) shows the calculation results of the heat loss rate under the conditions of Tair=20°C and Vair=0 m / s using the measurement device 6. FIG. 9(d) shows the calculation results of the heat loss rate under the conditions of Tair=20°C and Vair=5 m / s using the measurement device 6.

[0050] First, comparing Figure 9(a) and (b), the heat loss rate for measurement device 5 when Tair = 20°C and Vair = 0 m / s is 0.87%, while the heat loss rate for measurement device 5 when Tair = 20°C and Vair = 5 m / s is 26.1%, a significant increase. From this result, it can be seen that with measurement device 5, an increase in wind speed increases the unaccounted heat flow that moves directly from the skin to the air, which is one of the factors that contribute to core body temperature estimation errors.

[0051] 9(c) and (d), the heat loss rate for measuring device 6 when Tair = 20°C and Vair = 0 m / s is 8.25%, and the heat loss rate for measuring device 6 when Tair = 20°C and Vair = 5 m / s is 8.83%, maintaining a relatively low heat loss rate regardless of wind speed. This result shows that measuring device 6 can estimate core body temperature Tbody more accurately over a wider temperature range and wider wind speed range than measuring device 5.

[0052] Here, measurement device 5 generated an estimation error of up to 1.47°C, which is a large error that can interfere with measuring a person's core body temperature. In contrast, measurement device 6 suppressed the estimation error to a maximum of 0.048°C, which is smaller than the maximum allowable error (±0.2°C) of a typical electronic thermometer.

[0053] FIG. 10 shows the relationship between the shape of the probe cover and the probe body in the measurement device 6 and the error in the estimated value of the core body temperature. (a) of FIG. 10 shows the relationship between the thickness of the probe cover in the measurement device 6 and the error in the estimated value of the core body temperature. (b) of FIG. 10 shows the relationship between the diameter and thickness of the probe body in the measurement device 6 and the error in the estimated value of the core body temperature. The calculation in (a) of FIG. 10 was performed under the conditions of Tair = 20°C, Tbody = 37°C, Vin = 5 m / s, rsen = 15 mm, and tsen = 5 mm. The calculation in (b) of FIG. 10 was performed under the conditions of Tair = 20°C, Tbody = 37°C, Vin = 5 m / s, tcover1 = 5 mm, and tcover2 = 5 mm.

[0054] The calculation results in Figure 10(a) confirmed that the larger tcover1 or the smaller tcover2, the smaller the core body temperature estimation error, and the smaller tcover1 or the larger tcover2, the larger the core body temperature estimation error. Furthermore, the results in Figure 10(b) confirmed that the larger rsen or the smaller tsen, the smaller the core body temperature estimation error, and the smaller rsen or the larger tsen, the larger the core body temperature estimation error. Increasing tcover1 and decreasing tcover2 reduces the thermal resistance of the probe cover 62, which is thought to have the same effect as using a probe cover 62 with high thermal conductivity. Furthermore, increasing rsen and decreasing tsen reduces the thermal resistance of the probe body 11, which is thought to have the same effect as using a probe body 11 with high thermal conductivity.

[0055] Fig. 11 is a diagram showing the change over time in air temperature and wind speed during measurements by the measuring devices 5 and 6. Fig. 12 is a diagram showing the change over time in error in the estimated values ​​of core body temperature measured by the measuring devices 5 and 6 when the air temperature and wind speed are suddenly changed under the conditions shown in Fig. 11.

[0056] This calculation was performed under conditions simulating a common daily scenario: moving to an air-conditioned room after a prolonged stay in a hot environment. Specifically, the initial conditions were Tair = 35°C, Tbody = 37°C, Vin = 0 m / s, rsen = 15 mm, tsen = 5 mm, tcover1 = 5 mm, and tcover2 = 5 mm. A steady-state solution for the temperature distribution in the calculation domain was calculated. Then, between 60 and 180 seconds after the start of the calculation, the temperature was changed from 35°C to 20°C and the wind speed was changed from 0 m / s to 5 m / s. Furthermore, the time evolution of the error in the estimated core body temperature measured by each measurement device 5 and 6 was also calculated.

[0057] First, in measurements using measuring device 5 and measurements using measuring device 6 that do not take into account the heat capacity of the skin Cskin (i.e., measurements where Cskin = 0 in equation (2)), large estimation errors occur due to changes in temperature and wind speed, but it was confirmed that the errors then tend to gradually decrease.

[0058] FIG. 13 shows the time changes in the time derivatives of the skin temperature and the sensor temperature measured by each of the measuring devices 5 and 6. FIG. 14 shows an example of the spatial distribution of the magnitude of the time derivative of the temperature at the probes provided in each of the measuring devices 5 and 6. (a) of FIG. 14 shows the spatial distribution of the magnitude of the time derivative of the temperature at the probe 60 and its surroundings three minutes after the start of calculation. (b) of FIG. 14 shows the spatial distribution of the magnitude of the time derivative of the temperature at the probe 60 and its surroundings ten minutes after the start of calculation. (c) of FIG. 14 shows the spatial distribution of the magnitude of the time derivative of the temperature at the probe 60 and its surroundings thirty minutes after the start of calculation. (d) of FIG. 14 shows the spatial distribution of the magnitude of the time derivative of the temperature at the probe 50 and its surroundings three minutes after the start of calculation. (e) of FIG. 14 shows the spatial distribution of the magnitude of the time derivative of the temperature at the probe 50 and its surroundings ten minutes after the start of calculation. FIG. 14(f) shows the spatial distribution of the magnitude of the time derivative value of the temperature of the probe 50 and its surroundings 30 minutes after the start of the calculation.

[0059] For both measurement devices 5 and 6, it took approximately 30 minutes for the temperature field in the measurement area, including the skin temperature Tskin and the sensor temperature Tsen, to stabilize, and since there was a large temperature change at the start of the calculation, it is thought that the estimation error of the deep temperature increased due to the influence of the temperature change in measurements using measurement device 5 and measurements using measurement device 6 that do not take into account the heat capacity of the skin Cskin.

[0060] In contrast, in measurements using the measuring device 6 that take into account the heat capacity Cskin of the skin, the estimation error is reduced by compensating for temperature changes when estimating the core body temperature.

[0061] For example, the maximum error in the estimated value of deep body temperature was 7.23°C when the measurement by the measurement device 6 did not take the skin heat capacity Cskin into account, whereas the error was reduced by approximately 90% to 0.72°C when the measurement by the measurement device 6 took the skin heat capacity Cskin into account. Furthermore, the root mean square error (ROME) from the start of calculation up to 30 minutes after the start of calculation was 3.12°C when the measurement by the measurement device 6 did not take the skin heat capacity Cskin into account, whereas the error was reduced by approximately 95% to 0.15°C when the measurement by the measurement device 6 took the skin heat capacity Cskin into account. In other words, by performing measurements with the measurement device 6 taking the skin heat capacity Cskin into account, the estimation error of deep body temperature can be significantly reduced.

[0062] Furthermore, the time from 180 seconds after the start of calculation, when the air temperature and wind speed no longer change, until the estimated error in the deep body temperature falls within ±0.2°C is approximately 20 minutes and 20 seconds when the measurement by the measuring device 6 does not take the skin's heat capacity Cskin into account, whereas this is reduced to approximately 1 minute and 50 seconds when the measurement by the measuring device 6 takes the skin's heat capacity Cskin into account. In other words, by performing measurements with the measuring device 6 taking the skin's heat capacity Cskin into account, the time responsiveness of the measuring device 6 can be significantly improved.

[0063] 15(a) is a diagram showing the appearance of a prototype of the probe provided in the measurement device 6. The prototype is composed of a PDMS probe body with rsen=7.5 mm and tsen=5 mm, and aluminum sensor covers with tcover1=5 mm and tcover2=2.5 mm.

[0064] To evaluate the performance of the prototype, an experimental system was created that simulated biological tissue with a core body temperature. In this experimental system, a 10 mm thick ethylene propylene rubber, a material with a thermal conductivity similar to that of skin, was placed directly above a heater that simulated core body temperature and maintained a nearly constant temperature, and the prototype was placed on top of that.

[0065] Figure 15(b) shows the change in wind speed over time during measurements using the prototype. As shown in Figure 15(b), the prototype's estimated core body temperature was evaluated while gradually changing the airflow using a fan directly above the prototype. The estimated core body temperature was calculated by substituting the temperature sensor measurements taken by the prototype into equation (2). The unknown parameters derived from skin tissue included in equation (2) were determined based on measurement data when there was no wind, so as to minimize the estimation error.

[0066] Figure 15(c) shows the time variation of the estimated and reference values ​​of core body temperature measured using the prototype. The reference value is the temperature of a heater that simulates core body temperature. Figure 15(c) shows that the estimated core body temperature measured using the prototype contains a relatively large error immediately after a large change in airflow, but is linked to the change in the reference value.

[0067] Figure 15(d) shows a Bland-Altman plot of the estimated and reference core body temperature values ​​measured using the prototype. Figure 15(d) confirms that, overall, the estimation error, including the error during airflow, was maintained within ±0.1°C. Furthermore, comparing the measurement error (average ±3SD) under each wind speed, the measurement error during an airflow of 1.4 m / s was 0.0135±0.0405°C, and the measurement error during an airflow of 4.4 m / s was 0.0120±0.0431°C, showing almost no effect of airflow on the measurement error. Based on these results, similar to the numerical analysis results, it was experimentally confirmed that the measurement device 6 is capable of measuring core body temperature with high accuracy even during airflow.

[0068] Next, a method for measuring core body temperature using the measurement device 1 according to the present disclosure will be described. Fig. 16 is a schematic cross-sectional view of the probe 10 provided in the measurement device 1. Fig. 16 also shows a thermal equivalent circuit of the probe 10 and its surrounding environment. Fig. 16 also shows a part of the human body (skin) that is the test object TG.

[0069] Here, like the measuring device 6, the measuring device 1 according to the present disclosure includes a probe cover 12 in addition to a probe main body 11. Therefore, the measuring device 1 according to the present disclosure can basically achieve the same effects as the measuring device 6. In other words, the measuring device 1 according to the present disclosure can measure the deep body temperature of the test subject TG with higher accuracy than the measuring device 5 and the like. Note that, like the measuring device 6, the measuring device 1 according to the present disclosure can also significantly reduce the estimation error of the deep body temperature by measuring the deep body temperature using equation (2) and the like, taking into account the heat capacity Cskin of the skin.

[0070] Equation (2) can be divided into equations (6), (7), and (8) as follows.

[0071]

number

number

number

[0072] Tskin and Tsen are measured by the temperature sensors 112 and 113 of the probe 10. On the other hand, α and β are determined from the results of measurement using, for example, a rectal thermometer, an esophageal thermometer, a swallowed thermometer to measure the temperature inside the digestive tract, or a tympanic thermometer. Alternatively, α and β may be determined based on the changes in Tskin and Tsen over time from the time the probe 10 contacts the test object TG. This will be explained in detail below.

[0073] Fig. 17 is a diagram for explaining a method for measuring core body temperature using a measurement device according to the present disclosure. Fig. 17(a) shows the time change of (Tskin,t-Tskin,0) / (Tskin,∞-Tskin,0) for a plurality of different α values. Here, Tskin,t represents Tskin at time t [s], Tskin,0 represents Tskin at time 0 [s], and Tskin,∞ represents Tskin in a stable state. As shown in Fig. 17(a), the time constant of (Tskin,t-Tskin,0) / (Tskin,∞-Tskin,0) changes according to α.

[0074] Figure 17(b) shows the time change of the proportionality constant α. The value of α is determined by comparing the T-α curve shown in Figure 17(b) with the actual measured value.

[0075] Figure 17(c) shows the time change of the estimation error of the core body temperature Tbody for several different β values. When the value of α determined in Figure 17(b) is substituted into equation (6), the proportionality constant β that minimizes the estimation error of the core body temperature Tbody is derived from equation (6). In this way, the proportionality constants α and β are determined.

[0076] <Modifications of the probe 10> Next, some modified examples of the probe provided in the measurement device 1 according to the present disclosure will be described with reference to Fig. 18. Fig. 18 is a schematic cross-sectional view showing some modified examples of the probe provided in the measurement device 1.

[0077] For reference, FIG. 18(a) shows the probe 10 before deformation.

[0078] 18(b) shows a probe 10b which is a first modified example of the probe 10. In the probe 10b, the thickness of the top plate of the probe cover 12 (the part that covers the upper surface of the probe body 11; corresponding to tcover2) is thinner than in the probe 10. This allows the probe 10b to be lighter and less expensive.

[0079] FIG. 18(c) shows a probe 10c, which is a second modified example of the probe 10. In the probe 10c, the top plate and cylindrical side plate (corresponding to tcover1) of the probe cover 12 are thinner than those of the probe 10. This allows the probe 10c to be lighter and less expensive.

[0080] FIG. 18(d) shows a probe 10d, which is a third modification of the probe 10. In the probe 10d, the top plate and cylindrical side plate of the probe cover 12 are thinner than those of the probe 10. This allows the probe 10d to be lighter and less expensive. Furthermore, in the probe 10d, the probe cover 12 is provided so that a space is formed between the probe cover 12 and the side of the probe body 11. This allows the probe 10d to be lighter and less expensive without deforming the outer shape of the probe 10. Furthermore, in the probe 10d, the end of the probe cover 12, which is the contact surface with the test subject TG, is provided so as to extend along the test subject TG. This allows the contact surface between the probe cover 12 and the test subject TG to be kept large, allowing the probe 10d to be lighter and less expensive without degrading the accuracy of the core body temperature estimation.

[0081] FIG. 18(e) shows a probe 10e, which is a fourth modified example of the probe 10. In the probe 10e, the thickness of the top plate and cylindrical side plate of the probe cover 12 is thinner than in the probe 10. This allows the probe 10e to be lighter and less expensive. Furthermore, in the probe 10e, the end of the probe cover 12, which is the contact surface with the test subject TG, is arranged to extend along the test subject TG. This allows the contact surface between the probe cover 12 and the test subject TG to be kept large, allowing the probe 10e to be lighter and less expensive without deteriorating the accuracy of estimating the core body temperature.

[0082] FIG. 18(f) shows a probe 10f, a fifth modification of the probe 10. In the probe 10f, the top plate and cylindrical side plate of the probe cover 12 are thinner than those of the probe 10. This allows the probe 10f to be lightweight and inexpensive. Furthermore, in the probe 10f, the probe cover 12 is provided so as to form a space between the top plate and the side of the probe body 11. This allows the probe 10f to be lightweight and inexpensive without significantly deforming the outer shape of the probe 10. Furthermore, in the probe 10f, the end of the probe cover 12, which is the contact surface with the test subject TG, is provided so as to extend along the test subject TG. This allows the contact surface between the probe cover 12 and the test subject TG to be kept large, allowing the probe 10f to be lightweight and inexpensive without degrading the accuracy of core body temperature estimation. Furthermore, in the probe 10f, the corners between the top plate and the side plate of the probe cover 12 are chamfered. This allows the probe 10f to have improved aesthetics and usability.

[0083] Fig. 19 is a diagram showing errors in the estimated value of deep body temperature when each of the probes 10, 10a to 10f is used. In Fig. 19, the horizontal axis represents the weight of the entire probe, and the vertical axis represents errors in the estimated value of deep body temperature.

[0084] As shown in Figure 19, probes 10d, 10e, 10f, etc., which have a thin probe cover but have the same contact surface between the probe cover and the test subject TG as probe 10, are lightweight without degrading the accuracy of estimating core body temperature.

[0085] FIG. 20 is a diagram showing the time variation of the estimated core body temperature and the actual measured core body temperature (rectal temperature) measured by the measurement device 1 according to the present disclosure. In the example of FIG. 20, probe 10d is used. (a) of FIG. 20 shows the time variation of the estimated core body temperature and the actual measured core body temperature (rectal temperature). (b) of FIG. 20 shows the time variation of the difference between the estimated value and the actual measured value. As shown in FIG. 20, the estimation error of the core body temperature measured by the measurement device 1 according to the present disclosure is limited to a range of about ±0.1°C.

[0086] <Method of measuring cardiac potential> The measurement device 1 according to the present disclosure can measure not only the core body temperature of the test subject TG but also the cardiac potential of the test subject TG. Specifically, the measurement device 1 uses the second arithmetic processing unit 202 of the arithmetic processing circuit 20 to calculate an estimated value of the cardiac potential of the test subject TG based on the potential difference between the electrical signals obtained from the electrical conductors 121 and 122. The measurement device 1 can also extract the heart rate from the calculated cardiac potential using an existing algorithm. Furthermore, the measurement device 1 can also extract other feature quantities of the cardiac potential (e.g., heartbeat oscillation, HF / LF, respiratory rate, etc.) from the calculated cardiac potential using an existing algorithm.

[0087] Fig. 21 is a diagram showing changes over time in cardiac potential measured by the measurement device 1 according to the present disclosure. (a) of Fig. 21 shows changes over time in the measured values ​​of cardiac potential. (b) of Fig. 21 shows changes over time in the heart rate extracted from the measured values ​​of cardiac potential. As shown in Fig. 21, the cardiac potential and heart rate measured by the measurement device 1 according to the present disclosure are kept within a predetermined error range.

[0088] <Method for measuring sweat rate> The measurement device 1 according to the present disclosure not only measures the core body temperature and cardiac potential of the test subject TG, but also measures the amount of sweat produced by the test subject TG. Specifically, the measurement device 1 uses the third arithmetic processing unit 203 of the arithmetic processing circuit 20 to calculate an estimated value of the amount of sweat produced by the test subject TG based on the detection result of the temperature sensor 112 and the calculation result (i.e., the estimated value of the core body temperature) by the first arithmetic processing unit 201.

[0089] For example, the arithmetic processing circuit 20 calculates the amount of sweat (sweat rate SW(t)) of the test subject TG using the following equation (9).

[0090]

number

[0091] Here, ΔTskin(t) represents the difference between the skin temperature Tskin and the initial temperature. ΔTbody(t) represents the difference between the core temperature Tbody and the initial temperature. PI represents the insensible perspiration value [g / min]. αij, βij (i, j are either 0 or 12) represent coefficients. PI, αij, βij are set to predetermined values ​​using existing methods.

[0092] 22 is a diagram showing the time variation of the estimated value of the sweat rate measured by the measuring device 1 according to the present disclosure and the actual measured value of the sweat rate. As shown in FIG. 22, the estimated value of the sweat rate measured by the measuring device 1 according to the present disclosure is kept within a predetermined error range compared to the actual measured value.

[0093] As described above, the measuring device 1 according to the present disclosure can simultaneously measure multiple types of test contents for the test subject TG. Because the measuring device 1 according to the present disclosure can measure multiple types of test contents using a single probe, it can achieve weight reduction and cost reduction. Furthermore, the measuring device 1 according to the present disclosure can significantly reduce the estimation error of the core body temperature by measuring the core body temperature while taking into account the heat capacity of the skin of the test subject TG.

[0094] (Hardware configuration for realizing the measurement processing function of the measurement device 1) The measurement process performed by the measurement device 1 can be realized by a general-purpose computer system, which will be briefly explained below with reference to FIG.

[0095] 23 is a block diagram showing an example of a hardware configuration that realizes the measurement processing function of the measurement device 1. The computer 300 includes, for example, a CPU (Central Processing Unit) 301, which is a control device, a RAM (Random Access Memory) 302, and a ROM (Read Only Memory) 303. The computer 300 further includes an IF (Interface) 304, which is an interface with the outside, and an HDD (Hard Disk Drive) 305, which is an example of a non-volatile storage device. Furthermore, the computer 300 may include other components not shown, such as input devices such as a keyboard and a mouse, and a display device such as a display.

[0096] The HDD 305 stores an OS (Operating System) (not shown) and a control program 306. The control program 306 is a computer program in which the measurement process of the measurement device 1 is implemented.

[0097] The CPU 301 controls various processes in the computer 300, access to the RAM 302, the ROM 303, the IF 304, and the HDD 305, etc. In the computer 300, the CPU 301 reads and executes the OS and the control program 306 stored in the HDD 305. In this way, the computer 300 realizes the measurement processing function of the measurement device 1.

[0098] The above-mentioned program includes instructions (or software code) that, when loaded into a computer, cause the computer to perform one or more functions described in this disclosure. The program may be stored on a non-transitory computer-readable medium or a tangible storage medium. By way of example and not limitation, computer-readable medium or tangible storage medium includes RAM, ROM, flash memory, solid-state drive (SSD) or other memory technology, CD-ROM, digital versatile disc (DVD), Blu-ray disc or other optical disk storage, magnetic cassette, magnetic tape, magnetic disk storage or other magnetic storage device. The program may also be transmitted on a transitory computer-readable medium or communication medium. By way of example and not limitation, transitory computer-readable medium or communication medium includes electrical, optical, acoustic, or other forms of propagated signals.

[0099] Although the present disclosure has been described above with reference to the embodiments, the present disclosure is not limited to the above-described embodiments. Various modifications that can be understood by those skilled in the art can be made to the configuration and details of the present disclosure within the scope of the present disclosure. Furthermore, each embodiment can be combined with other embodiments as appropriate.

[0100] Each drawing is merely an example for describing one or more embodiments. Each drawing may relate not only to one particular embodiment, but also to one or more other embodiments. As will be understood by those skilled in the art, various features or steps described with reference to any one drawing can be combined with features or steps shown in one or more other drawings to create, for example, an embodiment not explicitly shown or described. Not all features or steps shown in any one drawing are necessary to describe an exemplary embodiment, and some features or steps may be omitted. The order of steps described in any drawing may be changed as appropriate. [Explanation of symbols]

[0101] 1. Measuring device (multimodal sensor) 10 probes 10a~10f probe 11 Probe body 12 Probe cover 20 Arithmetic processing circuit 111 Insulation 112 Temperature sensor (first temperature sensor) 113 Temperature sensor (second temperature sensor) 121 Electrical Conductor (First Electrical Conductor) 122 Electrical Conductor (Second Electrical Conductor) 123 Insulator 201 First processing unit 202 Second processing unit 203 Third processing unit 300 Computers 301 CPU 302 RAM 303 ROM 304 IF 305 HDD 306 Control Program

Claims

1. Heat insulation material, a first temperature sensor provided on the bottom surface of the heat insulating material, which is the surface that comes into contact with the living body being tested; a second temperature sensor provided on the top surface of the heat insulating material, the top surface facing the bottom surface of the heat insulating material; a first electrical conductor having a contact surface with the test object and provided so as to cover at least a portion of a side surface of the thermal insulating material; a second electrical conductor having a contact surface with the test object, covering at least another part of the side surface of the thermal insulating material, and electrically separated from the first electrical conductor; a first calculation processing unit that calculates a core body temperature of the test subject based on the detection results of the first temperature sensor and the second temperature sensor; a second arithmetic processing unit that calculates a cardiac potential of the test subject based on the electrical signals obtained from the first electrical conductor and the second electrical conductor; A measuring device equipped with:

2. The apparatus further includes a third arithmetic processing unit that calculates the amount of sweat of the test subject based on the detection result of the first temperature sensor and the calculation result of the first arithmetic processing unit. The measurement device according to claim 1 .

3. The heat insulating material has a cylindrical shape. The measurement device according to claim 1 .

4. The heat insulating material is made of PDMS. The measurement device according to claim 1 .

5. the first electrical conductor and the second electrical conductor are made of a material having a higher thermal conductivity than the thermal insulating material. The measurement device according to claim 1 .

6. The first electrical conductor and the second electrical conductor are both made of Al, Cu, or an alloy containing either Al or Cu. The measurement device according to claim 1 .

7. The probe further includes an insulator provided between the first electrical conductor and the second electrical conductor, and provided to cover the side and top surfaces of the thermal insulating material together with the first electrical conductor and the second electrical conductor as a probe cover. The measurement device according to claim 1 .

8. The insulator is made of a material having a higher thermal conductivity than the heat insulating material. The measurement device according to claim 7.

9. The insulator is made of either AlN or SiC. The measurement device according to claim 7.

10. The probe cover is provided so as to form a space region between the probe cover and a side surface of the thermal insulating material. The measurement device according to claim 7.

11. The probe cover is provided so that an end portion, which is a contact surface with the test object, extends along the test object. The measurement device according to claim 7.

12. Heat insulation material, a first temperature sensor provided on the bottom surface of the heat insulating material, which is the surface that comes into contact with the living body being tested; a second temperature sensor provided on the top surface of the heat insulating material, the top surface facing the bottom surface of the heat insulating material; a first electrical conductor having a contact surface with the test object and provided so as to cover at least a portion of a side surface of the thermal insulating material; a second electrical conductor having a contact surface with the test object, covering at least another part of the side surface of the thermal insulating material, and electrically separated from the first electrical conductor; A measurement method using a measurement device comprising: Calculating a core body temperature of the test subject based on the detection results of the first temperature sensor and the second temperature sensor; calculating a cardiac potential of the test subject based on the electrical signals obtained from the first electrical conductor and the second electrical conductor; Measurement method.

13. further calculating the amount of sweat of the test subject based on the detection result of the first temperature sensor and the calculated core body temperature; The measurement method according to claim 12.

14. Heat insulation material, a first temperature sensor provided on the bottom surface of the heat insulating material, which is the surface that comes into contact with the living body being tested; a second temperature sensor provided on the top surface of the heat insulating material, the top surface facing the bottom surface of the heat insulating material; a first electrical conductor having a contact surface with the test object and provided so as to cover at least a portion of a side surface of the thermal insulating material; a second electrical conductor having a contact surface with the test object, covering at least another part of the side surface of the thermal insulating material, and electrically separated from the first electrical conductor; A control program for causing a computer to execute a measurement process using a measurement device comprising: A process of calculating a core body temperature of the test subject based on the detection results of the first temperature sensor and the second temperature sensor; calculating a cardiac potential of the test subject based on electrical signals obtained from the first electrical conductor and the second electrical conductor; A control program that causes a computer to execute the above.

15. and further causing the computer to execute a process of calculating the amount of sweat of the test subject based on the detection result of the first temperature sensor and the calculated deep body temperature. The control program according to claim 14.

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