CN104586407B - Multi-parameter physiological indication detection device and detection method thereof - Google Patents

Abstract

A multi-parameter physiological indication detection device and a detection method thereof belong to the technical field of medical device detection equipment. The measuring device includes a probe and a host. The probe includes a multi-parameter integrated signal acquisition component, a heat transfer component, and a heat dissipation component; the host includes a data processing module and a tablet computer; Parameter signals such as blood flow velocity and other parameters are input to the host computer, and the data analysis and calculation are performed by the data processing module. The tablet computer controls the timing of the signal acquisition by the data processing module and realizes human-computer interaction, and finally the test result is displayed by the tablet computer. The invention can measure many physiological parameter indexes such as environment temperature and humidity, body surface temperature and humidity, pulse, blood oxygen saturation, blood flow velocity, hemoglobin concentration, etc., and realizes high integration of products. In particular, the device can non-invasively measure the blood glucose concentration of the human body through the above parameters.

Description

A multi-parameter physiological indication detection device and detection method thereof

technical field

The invention relates to a physiological indication detection instrument, which belongs to the technical field of medical instrument detection equipment.

Background technique

Inquire about relevant medical device registration products in the State Food and Drug Administration, and found that there are no domestic or imported medical devices that non-invasively measure blood sugar, hemoglobin, blood flow velocity and other parameters in China, and the more common products can only be tested One or two physiological parameters, such as blood glucose meter (invasive or minimally invasive), hemoglobin meter (invasive or minimally invasive), pulse oximeter (noninvasive), etc. Although invasive and minimally invasive measurement methods have a high accuracy rate, there is a certain risk of infection because of the need to take blood samples, and they also bring a lot of pain to patients. Therefore, it is of great significance to study a non-invasive multi-parameter medical device.

Devices for non-invasive detection of blood oxygen saturation have been used, such as the non-invasive measurement of blood oxygen saturation using spectral analysis in the patent document CN1011O3921A (a method and device for measuring blood oxygen saturation). Its theoretical basis is Lambert-Beer's law. Two kinds of photodiodes emitting different spectra are placed on the same side of the detected part, and a photoelectric receiving device is placed on the other side of the measured part, and then the blood oxygen saturation is calculated according to the AC component ratio of the two photocurrents obtained. There are still some problems in the non-invasive measurement of hemoglobin concentration, such as the interference of components in tissues, resulting in low accuracy.

Non-invasive measurement of human blood glucose concentration is still a challenge. Many scholars have proposed many methods based on different principles, among which the US patent (US.Pat.NO.5975305; US.Pat.NO.20060094941) is the first to realize a thermal-optical non-invasive blood glucose detection method based on the thermal integration of metabolic rate . This method assumes that the heat in the body comes from the energy released by metabolism, and the main energy source of metabolism is sugar, and most tissue cells generate and obtain energy through the aerobic oxidation process of glucose. Since the (static) heat production and heat dissipation are numerically equal in equilibrium, blood glucose levels can be estimated by measuring physiological parameters such as total blood oxygen and heat dissipation.

U.S. Patents (US.Pat.NO.5795305 and US.Pat.NO.5924996) and Hitachi Manufacturing Co., Ltd. of Japan have proposed a patent (Patent No. ZL 03178742.8) to obtain blood sugar by detecting skin temperature, and need to go through blood Oxygen saturation and blood flow volume are corrected to obtain stable measurement data. The measurement principle of this blood glucose level determination equipment is also based on the thermal metabolism integration method, and its composition includes: 1. Calorie measurement device: used to measure multiple body surface temperatures and ambient temperature to obtain and calculate the heat dissipated from the body surface Information about heat transfer by convection heat transfer and heat transfer by radiation; 2. Oxygen volume measurement device: used to obtain information about blood oxygen volume; 3. Optical measurement device: used to calculate hemoglobin concentration and hemoglobin oxygen saturation.

The above-mentioned patented technology has the following problems: First, the human-computer interaction function is weak, the operation is inconvenient, and the detection data cannot be stored for a long time, and it is difficult to realize the regular correction of the data; the second is that the detection accuracy of some parameters is not high, and the accuracy of parameter detection needs to be further improved and sensitivity; the third is that the measured parameters are relatively single, and there is no effective integration of various test parameters.

Contents of the invention

The purpose of the present invention is to provide a multi-parameter physiological indication detection device and testing method, enhance the human-computer interaction function of the physiological testing instrument, improve the parameter measurement accuracy, and overcome the defect of a single test parameter.

Technical scheme of the present invention is as follows:

A multi-parameter physiological indication detection device, the device includes a probe and a host, and wired or wireless communication is used between the probe and the host; the probe includes a multi-parameter integrated signal acquisition component, a heat transfer component and a heat dissipation component; the multi-parameter The integrated signal acquisition component includes an infrared radiation sensor for detecting body surface and ambient temperature parameters, a humidity sensor for detecting environment and body surface humidity parameters, an infrared light emitting array, an infrared light receiver, and a proximity sensor for detecting blood flow parameters. terminal thermistor and remote thermistor; the host computer includes a data processing module, and the data processing module includes a microprocessor, a signal conditioning unit and a storage unit; the signal conditioning unit includes an amplification filter circuit, an A/D conversion circuit and integral circuit; the signal collected by the multi-parameter integrated signal acquisition part is processed by the signal conditioning unit and then sent to the microprocessor, and the microprocessor calculates and processes the signal, and sends the calculation result to the storage unit for storage; the infrared light emitting array and The output line connection of the microprocessor is characterized in that: the host computer also includes a tablet computer, and the tablet computer includes a communication protocol module, a physiological parameter detection module, a user interaction module and a touch display screen; the tablet computer and the data processing module pass a serial The interface connection realizes two-way communication; the physiological parameter detection module transmits the obtained results to the user interaction module and displays them on the touch screen to realize the human-computer interaction function.

The multi-parameter physiological indication detection device is characterized in that: the tablet computer adopts an Android operating system tablet computer with an ARM architecture.

The multi-parameter physiological indication detection device is characterized in that: the heat dissipation component adopts a heat dissipation fin, and the heat dissipation fin is a comb-tooth plate structure.

The multi-parameter physiological indication detection device is characterized in that the probe adopts a clip-type structure.

The multi-parameter physiological indication detection device is characterized in that: the heat transfer component adopts a heat transfer rod, and the heat transfer rod adopts a cross structure, a nail structure, a dumbbell structure, a cylinder or a hexahedron structure.

The multi-parameter physiological indication detection device is characterized in that: the top of the heat transfer rod is coated with a gold layer.

A multi-parameter physiological indication detection method of the device, characterized in that the method comprises the following steps:

1) The physiological parameter detection module sends instructions through the serial interface, and controls the microprocessor to collect signals;

₂ ) Before putting the probe into the measured part, the ambient temperature value T1 is obtained through the remote thermistor and the infrared radiation sensor, and the ambient humidity H1 is obtained through the humidity sensor _;

3) After the measured part is put into the probe, the temperature value T2 of the human body is obtained through the proximal thermistor, and the humidity _H2 of the human body is obtained through the humidity sensor _;

4) Measure the blood oxygen saturation and pulse of the human body: emit four wavelengths of infrared light through the infrared light emitting array, the wavelengths are 660nm, 730nm, 800nm and 940nm, and use the infrared receiver to receive the optical signal after passing through the measured part. Use the formula (1) to get the blood oxygen saturation of the human body:

SpO ₂ =α ₂ ×R ² +α ₁ ×R+α ₀ (1)

Among them, SpO ₂ is the oxygen saturation of human blood, α ₀ =100.72, α ₁ =10.28, α ₂ =-26.67, and They are the minimum value of the output light intensity of 660nm and 940nm wavelengths changing with the pulse, and They are the maximum value of the output light intensity at 660nm and 940nm wavelengths changing with the pulse;

According to the intensity of the emitted light Change the frequency to calculate the pulse Pulse;

5) Test the hemoglobin concentration Hgb: the relationship between the concentrations in the blood components is as shown in formula (2),

Among them, C ₀ is the blood concentration, CHb is the concentration of deoxygenated _hemoglobin , is the oxygen-bound hemoglobin concentration, is the water concentration, C _other is the concentration of the remaining components;

Solving equations (3), get _CHb and

in, S is the attenuation factor caused by the scattering of tissue components, because the concentration of the remaining components and the attenuation caused by scattering are relatively small, put As a constant, ε represents the absorption coefficient of the substance at a specific wavelength, I ₀ represents the light intensity of the incident light, I represents the light intensity after passing through the measured part, d _pef is the path correction factor at a specific wavelength, and the hemoglobin concentration

6) Calculation of blood flow BF: By testing the value of the proximal thermistor and the distal thermistor after being placed in the measured part, the temperature change curve at both ends of the heat transfer rod is obtained, and the difference between the average areas of the two curves is calculated , using the formula (4) to calculate the bleeding flow,

where BF is the blood flow, a _s′ and a _v are constants, T _j1 is the temperature at the near end of the heat transfer rod at the beginning of the test, T _j2 is the temperature at the end of the test at the near end of the heat transfer rod, t ₁ is the starting time point of valid data, t ₂ is the end time point of valid data, S ₁ is the average temperature at the proximal end of the heat transfer rod, and S ₂ is the average temperature at the far end of the heat transfer rod;

7) Calculation of blood sugar level: Considering the impact of people's height, weight and age on the model, the blood sugar level is calculated using formula (5):

G=f(H,BF,SpO ₂ ,Hgb,High,Weight,Age) (5)

Among them, H is the heat generated by human metabolism, which is calculated from the environment temperature and humidity, body temperature and humidity, blood flow, and pulse, H=g(T ₁ , T ₂ , H ₁ , H ₂ , BF, Pulse);

8) Store the data measured and calculated in steps 2) to 7) in the storage unit, and send them to the physiological parameter detection module through the serial interface, and the physiological parameter detection module sends the data to the user interaction module to realize the human-computer interaction function .

Compared with the prior art, the present invention has the following advantages and outstanding effects: ① select the Android platform to cooperate with the design of the human-computer interaction interface, on the one hand to make up for the weakness of digital signal processing (DSP) in developing the human-computer interface, on the other hand, based on Android The platform has excellent application interaction, strong scalability, short development cycle, and can easily develop client programs with good user experience; ②simultaneously detect multiple physiological parameters of the human body, realizing a high degree of integration of the detection system, and realizing Non-invasive measurement of concentration; ③Integrates various detection parameters such as ambient temperature and humidity, improves the shape and process of the heat transfer rod, and effectively improves the detection accuracy.

Description of drawings

Fig. 1 is a hardware block diagram of a multi-parameter physiological indicator detection device provided by the present invention.

Fig. 2 is a structural schematic diagram of a probe of a multi-parameter physiological indication detection device.

Figure 3 is a schematic diagram of the temperature measurement bridge.

Figure 4 is the variation of the absorption coefficient of deoxyhemoglobin, oxyhemoglobin and water with light frequency.

Figure 5 is a schematic diagram of the heat transfer method.

Figure 6 is an example of the signals at both ends of the heat transfer rod.

Fig. 7 is a schematic structural diagram of the heat transfer rod of the multi-parameter physiological indication detection device.

Fig. 8 is a schematic diagram of the heat sink structure (comb-teeth plate structure) of the multi-parameter physiological indication detection device.

Fig. 9 is a flow chart of the human-computer interaction of the multi-parameter physiological sign detection device.

In the figure: 1-top cover; 2-infrared light emitting array; 3-heat sink; 4-base; 5-circuit board; 6-infrared light receiver; 7-remote thermistor; 8-heat transfer rod; 9-proximal thermistor; 10-humidity sensor; 11-infrared radiation sensor; 12-lower contact seat plate; 81-gold layer.

detailed description

The present invention will be described in detail below in conjunction with the accompanying drawings and specific embodiments.

Fig. 1 is a hardware block diagram of a multi-parameter physiological indication detection device provided by the present invention, the multi-parameter physiological indication detection device includes a probe and a host; the probe includes a multi-parameter integrated signal acquisition component, a heat transfer component and a heat dissipation component; The multi-parameter integrated signal acquisition part includes an infrared radiation sensor 11, a humidity sensor 10, a near-end thermistor 9, a far-end thermistor 7, an infrared light emitting array 2 and an infrared light receiver 6; the infrared radiation sensor 11 is used to detect Body surface and ambient temperature parameters, humidity sensor 10 is used to detect environment and body surface humidity parameters; proximal thermistor 9, remote thermistor 7, infrared light emitting array 2 and infrared light receiver 6 are used to detect blood flow Parameters, the infrared light emitting array 2 and the infrared light receiver 6 are also used to detect pulse, blood oxygen saturation and hemoglobin parameters, and the detection parameters of the infrared radiation sensor 11 and humidity sensor 10 are used to calculate blood sugar parameters.

The host computer includes a data processing module and a tablet computer, and the data processing module includes a microprocessor, a signal conditioning unit and a storage unit; the microprocessor uses a DSP processing chip; the signal conditioning unit includes an amplification filter circuit, an A/ D conversion circuit and integration circuit; the storage unit includes an SD memory card; the signal collected by the multi-parameter integrated signal acquisition part is processed by the signal conditioning unit and sent to the microprocessor, and the signal is calculated and processed by the microprocessor, and the calculation result is calculated Send into storage unit storage; Infrared light emission array is connected with the output line of microprocessor; Described panel computer comprises communication protocol module, physiological parameter detection module, user interaction module and touch display screen, adopts the Android operating system of ARM framework; The communication protocol module realizes the command and data communication between the data processing module and the tablet computer; the physiological parameter detection module controls the multi-parameter detection sensor integration probe by controlling the data processing module, thereby realizing the multi-parameter detection sensor integration of each sensor in the probe The collection of data; the user interaction module is used to obtain the detection instructions given by the user, and obtain the results of the physiological parameter detection module through the communication protocol module; the touch display screen is used for all control operations and displays all detection parameters, including But not limited to ambient temperature and humidity, body surface temperature and humidity, pulse, blood oxygen saturation, blood flow velocity, hemoglobin concentration and blood sugar concentration.

The data processing module and the tablet computer are connected through a serial interface to realize two-way communication; the probe and the host are connected by wired or wireless communication to complete data transmission.

Fig. 2 is a structural schematic diagram of a probe of a multi-parameter physiological indication detection device, the probe adopts a clip structure, including a top cover 1, a base 4, an infrared light emitting array 2, a heat sink 3, a circuit board 5, an infrared light receiver 6, Far-end thermistor 7, heat transfer rod 8, near-end thermistor 9, humidity sensor 10, infrared radiation sensor 11, lower contact seat plate 12; described infrared light emitting array 2 and infrared light receiver 6 are located at the The two sides of the part are arranged oppositely; the proximal thermistor 9 is arranged at one end of the heat transfer rod 8 close to the measured part, and the distal thermistor 7 is arranged at the end of the heat transfer rod 8 away from the measured part The measured part of the human body is placed between the base 4 and the top cover 1; the infrared light emitting array 2 of the present invention is arranged in the top cover 1, and the infrared radiation sensor 11, the infrared light receiver 6 and the heat transfer rod 8 are arranged in the base 4 and arranged along the direction of the parts of the human body to be measured.

Fig. 9 is the workflow of the user interaction module in the tablet computer: start the program, display the main interface of the test; there are user guide, new user, user detection and help options in the main interface, and the user needs to create a new user when testing for the first time; When creating a new user, you need to enter the basic information of the user; after the creation of the user is completed or after clicking the user test, the user selection interface will appear, and select the user corresponding to this test; after that, you need to select the test status of the user, such as fasting, 2 hours after a meal, etc.; after that Start the test, DSP starts to supply power, check whether the DSP power supply is connected correctly, the host sends test instructions and user information to the DSP; DSP collects test environment information, if it finds that the environmental conditions are not suitable for continuing the test, it sends relevant results to the host to end this test ; If the environmental conditions are suitable, please put the user into the part to be tested (such as fingers, ears, etc.). The parameter test results are sent to the host and displayed on the tablet; the host sends a command to turn off the DSP power supply, and the test ends.

The specific work flow of signal acquisition is: DSP issues order, and detection probe starts to collect data, and what infrared radiation sensor 11 and humidity transducer 10 measure respectively at this moment is ambient radiation temperature and ambient humidity, and DSP checks whether the environmental parameters tested are suitable, If it is inappropriate to send a command to the host, terminate this test, if the environmental parameters are suitable, the detection probe will be clamped on the measured parts of the human body (such as fingers, ears, etc.), and the infrared radiation sensor 11 and the humidity sensor 10 measure respectively the human body. The measurement site radiates temperature signals and surrounding humidity signals. At the same time, the heat transfer rod 8 is in contact with the site to be measured (such as fingers, ears, etc.), and heat transfer occurs. The resistance value of the remote thermistor 7 will change, and the changed resistance signal is detected by the temperature detection circuit; the light wave emitted by the infrared light emitting array 2 passes through the measured part (such as a finger, ear, etc.) to generate transmission The spectrum signal A is received by the infrared receiver 6 .

Then, the signals measured by these measuring elements are divided into three channels and sent to the microprocessor: the radiation temperature signal of the measured part of the human body, the ambient radiation temperature signal, the humidity signal around the measured part, the ambient humidity signal and the pressure signal through the transmission line in turn. Enter the microprocessor through the amplification and filtering circuit and the A/D conversion circuit; the resistance signals of the near-end thermistor 9 and the far-end thermistor 7 enter the temperature detection circuit through the transmission line, and the resistance signal is converted into a temperature signal, and then the temperature signal Enter the microprocessor through the amplification and filtering circuit and A/D conversion circuit; the transmitted light intensity signals Al~A4 enter the microprocessor through the first-order amplification and filtering circuit, the integration circuit and the second-order amplification and filtering circuit in turn. The work of the infrared light-emitting array is controlled by the transmitter control circuit, which is connected to the DSP through the control circuit; the first-order amplification filter circuit is controlled by the potentiometer switch circuit, and the potentiometer switch circuit is connected to the DSP through the control circuit. connection; the second-order amplification filter circuit is directly connected to the DSP through the control line. In this way, the transmitter control circuit, the first-order amplification and filtering circuit and the second-order amplification and filtering circuit are all controlled by the DSP.

Under the participation and control of the DSP, all signals are transmitted to the DSP, and these signals obtain the final result according to the multi-parameter measurement and calculation method of the present invention.

The test method of each parameter is as follows:

(1) The measurement of ambient temperature and human body temperature is realized by a thermistor, and the resistance value of the thermistor will increase as the temperature rises, satisfying the relationship:

Among them, Rt is the resistance value _of the thermistor at T1 temperature _; R is the nominal resistance value of the thermistor at T2 normal temperature; B is the constant parameter of the thermistor.

Common resistors and thermistors are used to form the bridge shown in Figure 3. In the figure, R1, R2, and R3 are common resistors, RT is thermistor, V0 and V1 are the voltage values of the test points. When the temperature changes, the thermal The resistance value of the sensitive resistor changes, the resistance value of the ordinary resistor changes little, the difference between V0 and V1 changes, and the voltage difference is obtained through the amplification circuit and the AD conversion circuit, and then the temperature value of the environment and the human body is obtained.

(2) The humidity of the environment can be obtained through the humidity sensor. The humidity sensor already has a relatively mature sensor chip, and the output voltage value can be directly amplified and sampled.

(3) Measurement of human blood oxygen saturation and pulse: Measured by optical methods, the theoretical basis is the Lambert-Beer law, when the light shines on a substance, the incident light intensity I and the outgoing light intensity I ₀ have the following relation:

Take the logarithm of the ratio of I and I ₀ to obtain the optical density A, namely:

A=ln(I/I ₀ )=εcd

Emit four wavelengths of infrared light through the infrared light emitting array, the wavelengths are 660nm, 730nm, 800nm and 940nm respectively, use the infrared receiver to receive the optical signal after passing through the measured part, and use the formula (1) to obtain the human blood oxygen saturation ,

SpO ₂ =α ₂ ×R ² +α ₁ ×R+α ₀ (1)

Among them, SpO ₂ is the oxygen saturation of human blood, α ₀ =100.72, α ₁ =10.28, α ₂ =-26.67, and They are the minimum value of the output light intensity of 660nm and 940nm wavelengths changing with the pulse, and They are the maximum value of the output light intensity at 660nm and 940nm wavelengths changing with the pulse;

According to the intensity of the emitted light Change the frequency to calculate the pulse Pulse;

(4) Hemoglobin concentration

Water in human blood accounts for about 70% to 85%, and accounts for 11% to 15% of normal human hemoglobin concentration. It can be seen that the main components of human blood are water and hemoglobin. The percentage of other components in the blood is less than 19%. The following assumptions can be made:

(a) Blood is mostly composed of water and hemoglobin.

(b) Under normal circumstances, the density of blood is constant (under normal circumstances, the density of whole blood is 1.048g/ml, the density of red blood cells is 1.085g/ml, and the density of plasma is 1.019g/ml, and the change of plasma density is small).

(c) The light attenuation caused by scattering and the average optical path of the light passing through the blood vessel have little relationship with the wavelength. The relationship between the concentrations of blood components is shown in formula (2),

Among them, C ₀ is the blood concentration, CHb is the concentration of deoxygenated _hemoglobin , is the oxygen-bound hemoglobin concentration, is the concentration of water, and C _other is the concentration of the remaining components.

Due to the complexity of human tissue, there is a strong scattering phenomenon for light. A large number of statistical results show that due to the influence of scattering, photons migrate randomly from the incident light source to the photodetector, and the total propagation path of light is "bow". type, so the Lambert-Beer law needs to be revised. The absorption law under strong scattering can be approximated as:

Among them, S is the attenuation factor caused by tissue component scattering, d _pef is the light path correction factor, c is the concentration of the measured tissue component, d is the path length of light penetration, and ε is the light absorption coefficient of the tissue component.

Solving equation (3) to get _CHb and

in, S is the attenuation factor caused by the scattering of tissue components, because the concentration of the remaining components and the attenuation caused by scattering are relatively small, put As a constant, ε represents the absorption coefficient of the substance at a specific wavelength, I ₀ represents the light intensity of the incident light, I represents the light intensity after passing through the measured part, d _pef is the path correction factor at a specific wavelength, and the hemoglobin concentration Figure 4 shows the changes in the absorption coefficients of deoxyhemoglobin, oxyhemoglobin and water in the wavelength range of 700-1300nm. Four wavelengths of 660nm, 730nm, 800nm and 940nm are selected for measurement. According to the measured light intensity value, the hemoglobin concentration can be calculated.

(5) Blood flow is measured by heat transfer method

In Figure 5, thermistors are installed at both ends of the heat transfer rod, and the temperature of the heat transfer rod is lower than the tissue temperature. After one end of the heat transfer rod is in contact with the surface of the measured part, heat transfer will occur between the surface of the measured part and the heat transfer rod , so that the temperature of the measured part changes. The amount of temperature change at any point on the heat transfer rod depends on the amount of heat transfer from the measured site to the heat transfer rod, and the amount of heat transferred ultimately depends on the blood flow in the capillaries. Therefore, by measuring the temperature change at any point on the heat transfer rod, the bleeding flow rate can be extrapolated.

Figure 6 is the temperature change curve at both ends of the heat transfer rod calculated through the data collected by the sensor. The horizontal axis is time and the vertical axis is temperature value. Blood flow BF can be expressed by formula (4):

where BF is the blood flow, a _s′ and a _v are constants, T _j1 is the temperature at the near end of the heat transfer rod at the beginning of the test, T _j2 is the temperature at the end of the test at the near end of the heat transfer rod, t ₁ is the starting time point of valid data, t ₂ is the end time point of valid data, S ₁ is the average temperature at the proximal end of the heat transfer rod, and S ₂ is the average temperature at the far end of the heat transfer rod.

In the temperature test at both ends of the heat transfer rod, even if a high-precision circuit design is adopted, there is still a certain test error. The device uses the estimated value of the ambient temperature to correct the offset of each temperature sensor to improve the accuracy.

Figure 7 shows a heat transfer rod with thermistors installed at both ends. In order to test the blood flow more accurately, the shape of the heat transfer rod needs to be optimized. After simulation, it is better to use a cross-shaped structure. After a test is completed, the residual heat of the heat transfer rod needs to be dissipated as soon as possible so that the next test can be started as soon as possible. For this purpose, a comb-tooth plate heat sink is designed, as shown in Figure 8.

(6) Human blood glucose concentration is calculated using the metabolic heat integration method

Metabolic heat integrated blood glucose testing method was proposed by Ok Kyung Cho et al. in 2004. They believe that the glucose and oxygen in the blood enter the tissue cells under the action of the blood circulatory system, and then convert into energy, water and carbon dioxide through oxidation reactions. Most of the energy is converted into heat, and the converted heat is dissipated to the surrounding environment in two ways: convection and radiation. Therefore, the metabolic heat of the human body is a function of the blood sugar concentration and the oxygen supply and is positively correlated with the blood sugar concentration and the oxygen supply, and the metabolic heat can be predicted by testing the heat dissipation. Its theory holds that the constant body temperature is maintained by the balance of blood sugar oxidation heat production and heat dissipation, and makes the following assumptions:

1) The metabolic heat production and heat dissipation of the body can be regarded as equal under static conditions.

2) Metabolic heat production is a function of blood glucose concentration and oxygen supply.

3) Oxygen supply is a function of blood oxygen saturation and local tissue blood flow.

4) The heat dissipation of the human body is mainly completed by convection and radiation.

According to the hypothesis, it can be known that metabolic heat is a function of blood glucose concentration and oxygen supply, and oxygen supply is determined by blood oxygen saturation, hemoglobin concentration, and blood flow in local tissues. Therefore, metabolic heat production is the function of blood glucose concentration, blood oxygen saturation , a function of hemoglobin concentration and blood flow, and can be expressed as follows:

H=f ₀ (G,BF,SpO ₂ ,Hgb)

In the formula: H is metabolic heat, BF is blood flow, _SpO2 is blood oxygen saturation, Hgb is hemoglobin concentration, and G is blood glucose concentration. If the metabolic heat, blood oxygen saturation and blood flow are measured, the blood sugar value is calculated using the formula (5) considering the influence of the person's height, weight and age on the model:

G=f(H,BF,SpO ₂ ,Hgb,High,Weight,Age) (5)

Among them, H is the heat generated by human metabolism, which is calculated from the environment temperature and humidity, body temperature and humidity, blood flow, and pulse, H=g(T ₁ , T ₂ , H ₁ , H ₂ , BF, Pulse).

Claims (6)

1. The method is characterized in that a detection device adopted by the method comprises a probe and a host, wherein the probe and the host use wired or wireless communication; the probe comprises a multi-parameter integrated signal acquisition component, a heat transfer component and a heat dissipation component; the multi-parameter integrated signal acquisition component comprises an infrared radiation sensor (11) for detecting the body surface and environmental temperature parameters, a humidity sensor (10) for detecting the environmental and body surface humidity parameters, an infrared light emission array (2), an infrared light receiver (6), a near-end thermistor (9) and a far-end thermistor (7) for detecting the blood flow parameters; the host comprises a data processing module, and the data processing module comprises a microprocessor, a signal conditioning unit and a storage unit; the signal conditioning unit comprises an amplifying and filtering circuit, an A/D conversion circuit and an integrating circuit; the signals collected by the multi-parameter integrated signal collecting component are processed by the signal conditioning unit and then sent to the microprocessor, the microprocessor calculates the signals and sends the calculation results to the storage unit for storage; the infrared light emitting array is connected with an output circuit of the microprocessor, and is characterized in that: the host further comprises a tablet computer, wherein the tablet computer comprises a communication protocol module, a physiological parameter detection module, a user interaction module and a touch display screen; the tablet personal computer is connected with the data processing module through a serial interface to realize bidirectional communication;

the detection method comprises the following steps:

1) the physiological parameter detection module sends an instruction through a serial interface to control the microprocessor to collect signals;

2) before the probe is put in the tested part, the environmental temperature value T is obtained by the remote thermistor and the infrared radiation sensor₁Obtaining the ambient humidity H by a humidity sensor₁；

3) After the probe is placed in the tested part, the human body temperature value T is obtained through the near-end thermistor₂Obtaining the human body humidity H through a humidity sensor₂；

4) Measuring the blood oxygen saturation and pulse of a human body: the infrared light emitting array emits infrared light with four wavelengths, the wavelengths are respectively 660nm, 730nm, 800nm and 940nm, the infrared receiver is used for receiving optical signals penetrating through a detected part, and the formula (1) is used for obtaining the blood oxygen saturation of a human body:

SpO₂＝α₂×R²+α₁×R+α₀(1)

wherein, SpO₂Is the oxygen saturation of human blood, α₀＝100.72,α₁＝10.28,α₂＝-26.67， Andthe minimum value of the outgoing light intensity with the wavelength of 660nm and 940nm along with the pulse change respectively,andthe maximum values of the outgoing light intensity with the wavelength of 660nm and 940nm along with the pulse change are respectively;

according to the intensity of the emergent lightCalculating the change frequency to obtain Pulse;

5) test of hemoglobin concentration Hgb: the relationship between the concentrations in the blood components is shown in formula (2),

wherein, C₀As blood concentration, C_HbIn order to obtain the concentration of the deoxygenated hemoglobin,in order for the oxygen to bind to the hemoglobin concentration,is the water concentration, C_otherIs the concentration of the remaining components;

solving the equation set (3) to obtain C_HbAnd

wherein,s is an attenuation factor caused by scattering of tissue components, and the attenuation caused by scattering and the concentration of residual components is relatively smallRegarded as a constant, representing the absorption coefficient of a substance at a particular wavelength, I₀Indicating the intensity of incident light, I indicating the intensity after passing through the site to be measured, d_pefIs a path correction factor at a particular wavelength;

concentration of hemoglobin

6) Calculating the blood flow BF: obtaining temperature change curves at two ends of the heat transfer rod by testing the near-end thermistor and the far-end thermistor after being placed in the tested part, calculating the difference value of the average areas of the two curves, calculating the blood flow by using a formula (4),

wherein, BF is the blood flow rate,a_s′、a_vis a constant, T_j1Is the temperature, T, of the proximal end of the heat transfer rod at the start of the test_j2Is the temperature of the proximal end of the heat transfer rod at the end of the test, t₁For a valid data start time point, t₂As the end time point of the valid data,S₁is the average value of the temperature at the near end of the heat transfer rod, S₂To transmitAverage value of the temperature at the far end of the hot bar;

7) calculating the blood sugar value: the blood glucose value is calculated by equation (5) taking into account the influence of the person's height, weight, age on the model:

G＝f(H,BF,SpO₂,Hgb,High,Weight,Age) (5)

wherein G is blood glucose concentration of human body, H is heat generated by metabolism of human body, BF is blood flow, SpO₂The blood oxygen saturation is shown, Hgb is the hemoglobin concentration, High is the height, Weight is the Weight, Age is shown; obtained by calculating the temperature, humidity, body temperature and humidity, blood flow and pulse, wherein H is g (T)₁,T₂,H₁,H₂BF, Pulse), wherein the meaning of the individual parameters is as described above;

8) and (3) storing the data obtained by measurement and calculation in the steps 2) to 7) into a storage unit, sending the data to a physiological parameter detection module through a serial interface, and transmitting the obtained result to a user interaction module by the physiological parameter detection module and displaying the result on a touch display screen to realize a man-machine interaction function.

2. A method for multi-parameter physiological indication detection as claimed in claim 1, wherein: the tablet computer adopts an android operating system of an ARM architecture.

3. A method for multi-parameter physiological indication detection as claimed in claim 1, wherein: the heat dissipation part adopts a heat dissipation fin which is of a comb flat plate structure.

4. A method for the detection of a multi-parameter physiological indication according to claim 1, 2 or 3, wherein: the probe adopts a clip type structure.

5. A method for the detection of a multi-parameter physiological indication according to claim 1, 2 or 3, wherein: the heat transfer component adopts a heat transfer rod, and the heat transfer rod adopts a cross structure, a nail structure, a dumbbell structure, a cylinder or a hexahedron structure.

6. The method for detecting a multi-parameter physiological indication according to claim 5, wherein: the top end of the heat transfer rod is plated with a gold layer (81).