Method and equipment for determining physiological parameters of host and medium

Abstract

The invention discloses a method and equipment for determining host physiological parameters and a medium. The method comprises the following steps: determining an impedance value of host tissue fluid according to a test current and a test voltage of a host physiological parameter detection device; determining the current body temperature of the host based on the impedance value and a fitting function between the impedance value and the body temperature of the host; and based on a compensation function between the host body temperature and the host physiological parameters, determining the host physiological parameters corresponding to the current host body temperature. According to the scheme, the accuracy of the host physiological parameter measurement result can be improved.

Description

Technical Field

[0001] The present application relates to the field of physiological monitoring technology, and in particular to a method, device and medium for determining physiological parameters of a host. Background Art

[0002] In the field of medical monitoring, accurate monitoring of host physiological parameters is of great significance for the prevention, diagnosis and treatment of diseases. Existing physiological parameter detection systems integrate temperature measurement modules to monitor body temperature while measuring physiological parameters so as to perform temperature compensation on physiological parameter readings. However, the temperature measurement module is often not in direct contact with the human body surface, but measures body temperature indirectly (such as through sensors inside the device). This indirect temperature measurement method causes a certain deviation between the measured body temperature and the actual body surface temperature. In addition, the temperatures measured by these systems are not obtained at the commonly used human body temperature measurement positions, which further increases the inaccuracy of temperature measurement. If the temperature measurement is inaccurate, the physiological parameter detection based on this inaccurate body temperature will not achieve the expected effect, resulting in deviations in the physiological parameter detection results. Summary of the invention

[0003] In order to solve the above problems, the present application proposes a method for determining host physiological parameters, comprising:

[0004] determining the impedance value of the host tissue fluid according to the test current and test voltage of the host physiological parameter detection device;

[0005] Determining the current body temperature of the host based on the impedance value and a fitting function between the impedance value and the host body temperature;

[0006] Based on the compensation function between the host body temperature and the host physiological parameter, the host physiological parameter corresponding to the current body temperature of the host is determined.

[0007] In one implementation of the present application, before determining the current body temperature of the host based on the impedance value and the fitting function between the impedance value and the host body temperature, the method further includes:

[0008] Collecting a plurality of first currents and first voltages of a host physiological parameter detection device, and a plurality of corresponding first host body temperatures;

[0009] determining an impedance value of host tissue fluid based on the first current and the first voltage, and determining a resistivity corresponding to the impedance value according to a mapping relationship between the impedance value and the resistivity;

[0010] Based on the resistivity and the corresponding first host body temperature, a preliminary fitting function between the resistivity of the host tissue fluid and the host body temperature is determined, and a fitting function between the impedance value and the host body temperature is determined in combination with the preliminary fitting function and the mapping relationship.

[0011] In one implementation of the present application, determining the current body temperature of the host based on the impedance value and a fitting function between the impedance value and the host body temperature includes:

[0012] Determining a ratio between a length and an average cross-sectional area of ​​a transmission path of the host physiological parameter detection device in the host tissue fluid;

[0013] The current body temperature of the host is determined according to the impedance value, the ratio, and a fitting function between the impedance value and the host body temperature.

[0014] In one implementation of the present application, determining the host physiological parameter corresponding to the current body temperature of the host based on a compensation function between the host body temperature and the host physiological parameter includes:

[0015] Based on the relationship between the host body temperature and the coefficient corresponding to the compensation function, a matrix transformation is performed on the current body temperature of the host to obtain a transformed body temperature matrix;

[0016] Based on the compensation function, the body temperature matrix, and the test voltage or the test current, a host physiological parameter corresponding to the current body temperature of the host is determined.

[0017] In one implementation of the present application, the compensation function includes a first compensation function and a second compensation function. Before determining the host physiological parameter corresponding to the current body temperature of the host, the method further includes:

[0018] Determining a coefficient corresponding to the first compensation function based on a first relationship function among the test voltage, the host body temperature, and the host physiological parameter;

[0019] or,

[0020] Based on a second relationship function among the test current, the host body temperature and the host physiological parameter, a coefficient corresponding to the second compensation function is determined.

[0021] In one implementation of the present application, before determining the host physiological parameter corresponding to the current body temperature of the host, the method further includes:

[0022] Acquiring reduction concentration information, reduction product coefficient and reducing agent coefficient of the host tissue fluid during the reaction; the reduction concentration information includes the reduction product concentration and the reducing agent concentration;

[0023] determining a difference between the reduction product coefficient and the reducing agent coefficient;

[0024] Determine a first proportional coefficient and a second proportional coefficient corresponding to the difference according to the correlation between the reduction concentration information and the host physiological parameter, the reduction product coefficient, and the reducing agent coefficient;

[0025] Determining a coefficient corresponding to the first compensation function according to a ratio between the first proportional coefficient and the second proportional coefficient and the difference value respectively;

[0026] The coefficients corresponding to the second compensation function are determined based on the coefficients corresponding to the first relationship function, in combination with the fitting function between the impedance value and the host body temperature, and the ratio between the length of the transmission path and the average cross-sectional area.

[0027] In one implementation of the present application, the first compensation function is:

[0028] lnG=α0+α1ΔU+α2ΔU 2 +…+α n ΔU n ;

[0029] The first relationship function is:

[0030]

[0031] Where G is the host physiological parameter; α0, α1, α2, ..., α n is the coefficient of the first compensation function; ΔU is the difference between the current test voltage and the initial test voltage of the electrode of the host physiological parameter detection device; R is the gas constant, n is the number of moles of electrons exchanged in the reaction, and F is the Faraday constant; C1 is the concentration of reduction products; C2 is the reducing agent concentration; a is the reduction product coefficient, b is the reducing agent coefficient, and T is the host body temperature.

[0032] In one implementation of the present application, the second compensation function is:

[0033] ln G=β0+β1I test +β2I test 2 +…+β n I test n ;

[0034] The second relationship function is:

[0035]

[0036] Where G is the host physiological parameter; β0, β1, β2, ..., β n I is the coefficient of the second compensation function;test A test current for a host physiological parameter detection device; R is the gas constant, n is the number of moles of electrons exchanged in the reaction, and F is the Faraday constant; C1 is the concentration of reduction products; C2 is the reducing agent concentration; a is the reduction product coefficient; b is the reducing agent coefficient; T is the host body temperature; L is the transmission path length; S is the average cross-sectional area of ​​the transmission path; A and B are the coefficients of the fitting function between the impedance value and the host body temperature.

[0037] The embodiment of the present application provides a device for determining a physiological parameter of a host, the device comprising:

[0038] at least one processor;

[0039] and, a memory communicatively coupled to the at least one processor;

[0040] The memory stores instructions executable by the at least one processor, and the instructions are executed by the at least one processor so that the at least one processor can perform a method for determining a host physiological parameter as described in any one of the above items.

[0041] The embodiment of the present application provides a non-volatile computer storage medium storing computer executable instructions, wherein the computer executable instructions are configured as follows:

[0042] A method for determining a host physiological parameter as described in any of the above items.

[0043] The method for determining the physiological parameters of a host proposed in the present application can bring the following beneficial effects: the present application directly analyzes the impedance value of the host tissue fluid and determines the body temperature by using the fitting function between the impedance value and the body temperature, thereby avoiding the limitation of the indirect measurement of the traditional temperature measurement module, reducing the temperature measurement deviation caused by the internal sensor of the device or the external environment temperature interference, and improving the accuracy of the host physiological parameter measurement on the premise that the measurement result is closer to the real body temperature of the host; in addition, compared with the traditional temperature measurement module, the present application directly reads the host body temperature rather than the compensated temperature, which improves the reading accuracy, and the temperature value obtained by the correspondence between the impedance value and the host body temperature has higher accuracy and sensitivity, which can not only more accurately reflect the slight changes in the host body temperature, but also provide more precise compensation for the physiological parameter detection, thereby improving the test performance of the entire detection device; in addition, by determining the host body temperature through the measurement and algorithm of the tissue fluid impedance, there is no need to use the chip temperature measurement module, which can reduce the overall power consumption to a certain extent, extend the battery life of the detection device, and reduce the need for frequent battery replacement or charging. BRIEF DESCRIPTION OF THE DRAWINGS

[0044] The drawings described herein are used to provide a further understanding of the present application and constitute a part of the present application. The illustrative embodiments of the present application and their descriptions are used to explain the present application and do not constitute an improper limitation on the present application. In the drawings:

[0045] Figure 1 A schematic diagram of a process for determining a host physiological parameter provided in an embodiment of the present application;

[0046] Figure 2 A schematic diagram of a simulated liquid experimental test connection provided in an embodiment of the present application;

[0047] Figure 3 A schematic diagram of a relationship of a preliminary fitting function provided in an embodiment of the present application;

[0048] Figure 4 A schematic diagram of a host body temperature monitoring principle provided in an embodiment of the present application;

[0049] Figure 5 A schematic diagram of the structure of a device for determining a physiological parameter of a host provided in an embodiment of the present application. DETAILED DESCRIPTION

[0050] In order to make the purpose, technical solution and advantages of the present application clearer, the technical solution of the present application will be clearly and completely described below in combination with the specific embodiments of the present application and the corresponding drawings. Obviously, the described embodiments are only part of the embodiments of the present application, not all of the embodiments. Based on the embodiments in the present application, all other embodiments obtained by ordinary technicians in this field without making creative work are within the scope of protection of the present application.

[0051] The technical solutions provided by various embodiments of the present application are described in detail below in conjunction with the accompanying drawings.

[0052] like Figure 1 As shown, a method for determining a host physiological parameter provided in an embodiment of the present application includes:

[0053] S101: Determine the impedance value of the host tissue fluid according to the test current and test voltage of the host physiological parameter detection device.

[0054] Host physiological parameters (such as blood glucose concentration) need to be measured by implanting a four-electrode electrochemical sensor into the host's subcutaneous tissue through a host physiological parameter detection device. The glucose-related enzymes attached to the electrodes will undergo an oxidation-reduction reaction with the glucose in the tissue fluid, and the blood glucose value is measured by the current generated between the electrodes. Since the operating environment temperature range of the continuous glucose detection system is 5 to 40°C, the final measurement value also needs to be temperature compensated. When performing temperature compensation, it is necessary to obtain the conversion relationship between the impedance value of the host tissue fluid and the host body temperature. The impedance value depends on the test current and test voltage generated when the host physiological parameter detection device is working.

[0055] When the host physiological parameter is blood glucose concentration, the corresponding specific calculation formula is:

[0056] G=kI test +C

[0057] Where G is the measured glucose value in human tissue fluid, in mmol / L; k is the gain coefficient, I test It is the current value generated by the quantitative electron gain and loss involved in the redox reaction measured by the test circuit connected to the sensor, and C is a constant term.

[0058] The current value I directly measured by the sensor is in the form of:

[0059] I=I test +I N

[0060] Where IN is the noise floor current.

[0061] IN can be eliminated by the auxiliary electrode (which is identical to the oxidation electrode except that it does not contain the reactants), so only I needs to be calibrated test The final host physiological parameters can be calibrated.

[0062] According to the general formula:

[0063]

[0064] Wherein, ΔU is the change in potential difference between the working electrode and the counter electrode caused by the redox reaction, which can be obtained by measuring and calculating the circuit connected to the sensor; R W-C It is the impedance value on the test path in the subcutaneous tissue of the human body.

[0065] ΔU=(U WE -U CE )-(U WE0 -U CE0 )

[0066] In the above formula, UWE and U CE are the working electrode and counter electrode potential values ​​when the redox reaction is stable as measured by the sensor; U WE0 and U CE0 are the potential values ​​of the initial working electrode and the counter electrode respectively. WE No change, only U CE Changes due to reduction reactions.

[0067] S102: Determine the current body temperature of the host based on the impedance value and a fitting function between the impedance value and the host body temperature.

[0068] After the impedance value of the host tissue fluid is determined, the host's current body temperature can be determined based on the impedance value and the fitting function between the impedance value and the host's body temperature. Compared with the traditional temperature measurement method, the fitting function reflects the corresponding relationship between the impedance value and the host's body temperature, which can effectively improve the test accuracy and test sensitivity.

[0069] According to the general resistance calculation formula:

[0070]

[0071] Among them, R W-C is the impedance value on the test path in the subcutaneous tissue of the human body, L and S are specifically the transmission path length of the working electrode and the counter electrode of the sensor in the tissue fluid and the average cross-sectional area on the transmission path, both of which are limited by the sensor model design. Therefore, the embodiment of the present application only considers the influence of the host body temperature on the conductivity σ, σ = 1 / ρ, ρ represents the resistivity of the host tissue fluid, based on the above relationship, the fitting function between the impedance value and the host body temperature can also be determined according to the preliminary fitting function between the resistivity and the host body temperature. Specifically, it can be carried out through the following steps:

[0072] Collecting a plurality of first currents and first voltages of a host physiological parameter detection device, and a plurality of corresponding first host body temperatures;

[0073] Determine an impedance value of the host tissue fluid based on the first current and the first voltage, and determine the resistivity corresponding to the impedance value according to a mapping relationship between the impedance value and the resistivity;

[0074] Based on the resistivity and the corresponding first host body temperature, a preliminary fitting function between the resistivity of the host tissue fluid and the host body temperature is determined, and a fitting function between the impedance value and the host body temperature is determined in combination with the preliminary fitting function and the mapping relationship.

[0075] Specifically, multiple first currents and multiple first voltages of the host physiological parameter detection device and multiple corresponding first host body temperatures are collected. The impedance value of the host tissue fluid is determined based on the first current and the first voltage, and the mapping relationship between the impedance value and the resistivity can be obtained according to the general resistance calculation formula, that is, When the impedance value is clear, the resistivity ρ corresponding to the impedance value can be determined. Based on the resistivity and the corresponding first host body temperature, the resistivity and the first host body temperature are fitted to determine the preliminary fitting function between the resistivity of the host tissue fluid and the host body temperature: Among them, A and B are the coefficients of the fitting function between the impedance value and the host body temperature, which are constants related to the solution characteristics. Their specific values ​​can be obtained by fitting the experimental data. Combining the above mapping relationship and the preliminary fitting function, the fitting function between the impedance value and the host body temperature can be determined. Among them, R W-C represents the impedance value, and T is the host body temperature.

[0076] In one embodiment, the fitting function between the impedance value and the host body temperature can be determined in the following manner. Figure 2 As shown in the schematic diagram of a simulated fluid experimental test connection, a simulated fluid is used to replace the host tissue fluid, and the main components are water, NaCl and other substances. First, the water bath and the high-precision heating / cooling circulation tank need to be connected as shown in the figure above, and the temperature sensor probe is placed on the fixture of the upper cover of the water bath, and the tissue fluid simulation fluid and water are introduced into the two water baths respectively. Then, the sensor is placed in the test fixture and placed on the fixture, and then connected to the test detection system PCBA. The sensor probe is inserted below the tissue fluid simulation liquid level, and the circulation tank temperature is adjusted to 20°C until the temperature sensor reading is stable. The detection system PCBA is connected to the main control device through Bluetooth technology, and the main control device sends the specified reading instruction, and the impedance between the sensor test electrodes is calculated through the PCBA, and the impedance value is fed back to the main control device. The temperature of the circulation tank is gradually increased to 45°C at intervals of 1°C, and the above temperature adjustment and impedance calculation process is repeated, and the data is summarized.

[0077] The obtained impedance values ​​and the first host body temperature are shown in Table 1:

[0078] Table 1

[0079]

[0080]

[0081] According to the sensor used in the test, the statistical value of L / S measured in a stable solution environment is 22.917*103 / m. According to the formula The resistivity and the first host body temperature data obtained after processing are shown in Table 2:

[0082] Table 2

[0083] Resistivity / Ω*m First host body temperature / ℃ Resistivity / Ω*m First host body temperature / ℃ 0.704 20 0.633 33 0.699 21 0.629 34 0.694 22 0.625 35 0.685 23 0.621 36 0.680 24 0.617 37 0.676 25 0.610 38 0.671 26 0.606 39 0.662 27 0.602 40 0.658 28 0.595 41 0.649 29 0.592 42 0.645 30 0.585 43 0.641 31 0.578 44 0.637 32 0.568 45

[0084] And σ=1 / ρ, its corresponding data with temperature are shown in Table 3:

[0085] Table 3

[0086]

[0087]

[0088] Based on the preliminary fitting function between resistivity and host body temperature Then there is Fit the data with a linear equation according to the preliminary fitting function to confirm the specific values ​​of A and B.

[0089] The fitting results are shown in Table 4:

[0090] Table 4

[0091]

[0092]

[0093] According to the data in Table 4, we can get Figure 3 The relationship diagram of the preliminary fitting function shown is given by Figure 3 It can be seen that: A = -2.9025, B = 748.32, the degree of fit is 0.9944, which can be regarded as the fitting effect is consistent with the theoretical situation.

[0094] After determining the fitting function between the impedance value and the host's body temperature according to the above preliminary fitting function and mapping relationship, the host's current body temperature can be obtained based on the detected impedance value analysis without a temperature sensor.

[0095] It should be noted that in other embodiments that can be implemented in the present application, the fitting function between the impedance value and the host body temperature can also be determined by fitting a certain number of actual measured values ​​of the host body temperature and the corresponding host tissue fluid impedance values.

[0096] In one embodiment, the ratio between the length of the transmission path of the host physiological parameter detection device in the host tissue fluid and the average cross-sectional area is determined, and the ratio is determined. After that, the impedance value calculated based on the test current and the test voltage and the ratio can be substituted into the fitting function between the impedance value and the host body temperature to finally determine the current body temperature of the host.

[0097] The schematic diagram of the existing host temperature monitoring principle is as follows Figure 4 As shown in the figure, when the NTC is attached to the sensor and implanted under the human skin, the change of the host's body temperature will cause the change of the thermistor. The processing chip in the monitoring system reads the current of the pin directly connected to the thermistor, and obtains the current resistance of the thermistor according to R=U / I. Then, the current host body temperature T can be obtained according to the resistance-temperature comparison table of the thermistor, and the data is finally transmitted to the mobile phone or PC. This method relies on the sensor reading provided by the temperature measurement module, but the final measured temperature is not the most direct surface temperature of the host, but the temperature after compensation. Finally, due to inaccurate temperature measurement results, the measurement accuracy of the host's physiological parameters will be reduced.

[0098] Compared with the prior art, the embodiment of the present application reads the host's internal temperature rather than the compensated temperature, which is less affected by the external environment temperature and is closer to the real body temperature. The host's current body temperature is determined based on the impedance value and the fitting function of the host's body temperature. This process replaces the chip temperature measurement module with the measurement value and algorithm, effectively improving the accuracy and sensitivity of the temperature measurement value, and reducing the overall power consumption of the host physiological parameter detection device.

[0099] S103: Determine the host physiological parameter corresponding to the host's current body temperature based on a compensation function between the host's body temperature and the host's physiological parameter.

[0100] The host body temperature is the analyte environment temperature. The more accurate the temperature measurement is, the more effective the monitoring reading of the host physiological parameters is, and the more accurate the output value is. Therefore, after obtaining the current body temperature of the host, the host physiological parameters need to be temperature compensated based on the compensation function between the host body temperature and the host physiological parameters, so as to obtain the host physiological parameters corresponding to the current body temperature of the host.

[0101] At a fixed temperature, it is assumed that the input and output values ​​of the sensor can be expressed by a polynomial function:

[0102] y=a0+a1x+a2x 2 +…+a n x n

[0103] Where x is the output value of the sensor, y is the true value of the physical quantity measured by the sensor, a0...a n Represents polynomial coefficients.

[0104] Converting the polynomial function into a matrix expression is:

[0105] M=(a0…a n )

[0106]

[0107] y=M·X

[0108] At this time, the influence of temperature t is considered, that is, a is a function of t. As in the above theory, a can also be expressed as a polynomial function of t:

[0109] a i (t) = b0 + b1t + b2t 2 +…b m t m

[0110] Among them, b0...b m Represents polynomial coefficients.

[0111] The final expression is:

[0112]

[0113] Converted into a matrix expression:

[0114] T=(tt 2 …t m )

[0115]

[0116] Then M=N·T, y=N·T·X.

[0117] Therefore, according to the above calculation process, the actual detection value of the host's physiological parameters can be considered as the multiplication value between multiple matrices, where T represents the body temperature matrix, which can be calculated based on the host's current body temperature, X is the voltage matrix or current matrix related to the test voltage or test current, and N is a matrix composed of the coefficients of the compensation function.

[0118] It should be noted that there are two compensation forms of compensation functions, one is temperature compensation based on test voltage, and the other is temperature compensation based on test current. The compensation functions in different compensation modes are also different. The first compensation function corresponding to the test voltage is expressed as:

[0119] lnG=α0+α1ΔU+α2ΔU 2 +…+α n ΔU n

[0120] Where G is the host physiological parameter; α0, α1, α2, ..., α n is the coefficient of the first compensation function; ΔU is the difference between the current test voltage and the initial test voltage of the electrode of the host physiological parameter detection device.

[0121] The second compensation function corresponding to the test current is expressed as:

[0122] lnG=β0+β1I test +β2I test 2 +…+β n I test n

[0123] Among them, β0, β1, β2,..., β n is the coefficient of the second compensation function; I test It is the test current of the host physiological parameter detection device.

[0124] The coefficients in the compensation function need to be solved to finally determine the body temperature matrix and the matrix N composed of the coefficients.

[0125] In one embodiment, the coefficients of the first compensation function are determined by testing a first relationship function between voltage, host temperature and host physiological parameters, and the coefficients of the second compensation function are determined by testing a second relationship function between current, host temperature and host physiological parameters.

[0126] The first relation function is:

[0127]

[0128] The second relationship function is:

[0129]

[0130] in, R is the gas constant, n is the number of moles of electrons exchanged in the reaction, and F is the Faraday constant; C1 is the concentration of reduction products; C2 is the reducing agent concentration; a is the reduction product coefficient, b is the reducing agent coefficient, and T is the host body temperature.

[0131] By comparing the relationship function and compensation function corresponding to the test voltage and test current respectively, it can be seen that the compensation function should have the same number of terms as the relationship function, both of which are two terms, and the relationship function is expressed in the form of functions related to the test voltage and test current respectively.

[0132] Therefore, the coefficients in the compensation function are α0 and α1, which are expressed in the following form:

[0133] In the first compensation function, the coefficients are

[0134] In the second compensation function, the coefficients are

[0135] It should be clear that in electrochemistry, the Nernst equation is used to calculate the equilibrium voltage of a specified redox pair at an electrode relative to the standard potential. It is specifically expressed as:

[0136]

[0137] Among them, E is the potential after the reaction stabilizes, EΦ is the potential in the initial state before the reaction starts, and Q is the reaction entropy.

[0138] The glucose redox reaction is expressed as follows: Glucose in the tissue fluid is converted into gluconic acid and hydrogen peroxide by glucose oxidase attached to the sensor electrode of the continuous glucose detection system. A reduction reaction occurs at the counter electrode CE, and the corresponding potential change is:

[0139]

[0140] Where C1 and C2 are the concentrations of the reduction product and the reducing agent, respectively, and a and b are the coefficients of the reduction product and the reducing agent in the relevant chemical reaction formula, respectively.

[0141] In one embodiment, based on the above reaction principle, when determining the coefficient of the compensation function, it can be determined by the reduction concentration information of the host tissue fluid during the reaction, the reduction product coefficient and the reducing agent coefficient. The reduction concentration information refers to the concentration of the reduction product and the reducing agent.

[0142] First, determine the difference ab between the reduction product coefficient and the reducing agent coefficient. Since C1 and C2 are related to the specific values ​​of the host physiological parameters, the specific correlation relationship is Next, according to the correlation, the reduction product coefficient and the reducing agent coefficient, the first proportional coefficient corresponding to the difference can be determined. And the second proportional coefficient alnk2-blnk3.

[0143] For the first compensation function, the first proportional coefficient and the second proportional coefficient are respectively divided by the difference, and the ratio finally calculated is the coefficient corresponding to the first compensation function.

[0144] For the second compensation coefficient, the coefficient corresponding to the second compensation function is determined according to the coefficient corresponding to the first relationship function, combined with the fitting function between the impedance value and the host body temperature, and the ratio between the length of the transmission path and the average cross-sectional area.

[0145] At this point, according to the above coefficients, a matrix N composed of corresponding coefficients can be obtained. The matrix N corresponding to the first compensation function is expressed as:

[0146]

[0147] The matrix N corresponding to the second compensation function is:

[0148]

[0149] In addition, based on the relationship between the coefficients in the compensation function and the host's body temperature, a matrix transformation is performed on the host's current body temperature to finally obtain the transformed body temperature matrix T.

[0150] In the first compensation function, the coefficient α is Therefore, the final transformed body temperature matrix is

[0151] In the second compensation function, the coefficient α is Therefore, the final transformed body temperature matrix is

[0152] X is divided into a voltage matrix related to the test voltage according to the selected compensation form or the current matrix related to the test current

[0153] In this way, based on the expression of the compensation function y=N·T·X, the host physiological parameters corresponding to the host's current body temperature can be determined through two different compensation methods according to the body temperature matrix and the test voltage or test current, and finally the temperature compensation of the host physiological parameters can be achieved, thereby improving the accuracy of the host physiological parameter detection results.

[0154] The above are embodiments of the method proposed in this application. Based on the same idea, some embodiments of this application also provide devices and non-volatile computer storage media corresponding to the above methods.

[0155] Figure 5 This is a schematic diagram of a device for determining a host physiological parameter provided in an embodiment of the present application. Figure 5 As shown, including:

[0156] at least one processor; and,

[0157] at least one processor is communicatively connected to a memory; wherein,

[0158] The memory stores instructions that can be executed by at least one processor, and the instructions are executed by at least one processor so that the at least one processor can execute a method for determining a host physiological parameter as described in any one of the above items.

[0159] The embodiment of the present application provides a non-volatile computer storage medium storing computer executable instructions, wherein the computer executable instructions are configured as follows:

[0160] A method for determining a host physiological parameter as described in any of the above items.

[0161] Each embodiment in this application is described in a progressive manner, and the same or similar parts between the embodiments can be referred to each other, and each embodiment focuses on the differences from other embodiments. In particular, for the device and medium embodiments, since they are basically similar to the method embodiments, the description is relatively simple, and the relevant parts can be referred to the partial description of the method embodiments.

[0162] The devices and media provided in the embodiments of the present application correspond one-to-one to the methods. Therefore, the devices and media also have similar beneficial technical effects as the corresponding methods. Since the beneficial technical effects of the methods have been described in detail above, the beneficial technical effects of the devices and media will not be repeated here.

[0163] Those skilled in the art will appreciate that the embodiments of the present application may be provided as methods, systems, or computer program products. Therefore, the present application may adopt the form of a complete hardware embodiment, a complete software embodiment, or an embodiment in combination with software and hardware. Moreover, the present application may adopt the form of a computer program product implemented in one or more computer-usable storage media (including but not limited to disk storage, CD-ROM, optical storage, etc.) that include computer-usable program code.

[0164] The present application is described with reference to the flowcharts and / or block diagrams of the methods, devices (systems), and computer program products according to the embodiments of the present application. It should be understood that each process and / or box in the flowchart and / or block diagram, as well as the combination of the processes and / or boxes in the flowchart and / or block diagram, can be implemented by computer program instructions. These computer program instructions can be provided to a processor of a general-purpose computer, a special-purpose computer, an embedded processor, or other programmable data processing device to generate a machine, so that the instructions executed by the processor of the computer or other programmable data processing device generate instructions for implementing the processes in the flowchart and / or block diagram. Figure 1 A process or multiple processes and / or boxes Figure 1 A device that provides the functions specified in a block or multiple blocks.

[0165] These computer program instructions may also be stored in a computer-readable memory capable of directing a computer or other programmable data processing device to operate in a specific manner, so that the instructions stored in the computer-readable memory produce an article of manufacture comprising an instruction device, which implements the process Figure 1 A process or multiple processes and / or boxes Figure 1A function specified in one or more boxes.

[0166] These computer program instructions can also be loaded onto a computer or other programmable data processing device so that a series of operating steps are executed on the computer or other programmable device to produce a computer-implemented process, thereby providing instructions for implementing the process. Figure 1 A process or multiple processes and / or boxes Figure 1 The steps for the functions specified in one or more boxes.

[0167] In a typical configuration, a computing device includes one or more processors (CPU), input / output interfaces, network interfaces, and memory.

[0168] The memory may include non-permanent storage in a computer-readable medium, random access memory (RAM) and / or non-volatile memory in the form of read-only memory (ROM) or flash RAM. The memory is an example of a computer-readable medium.

[0169] Computer readable media include permanent and non-permanent, removable and non-removable media that can be implemented by any method or technology to store information. Information can be computer readable instructions, data structures, program modules or other data. Examples of computer storage media include, but are not limited to, phase change memory (PRAM), static random access memory (SRAM), dynamic random access memory (DRAM), other types of random access memory (RAM), read-only memory (ROM), electrically erasable programmable read-only memory (EEPROM), flash memory or other memory technology, compact disk read-only memory (CD-ROM), digital versatile disk (DVD) or other optical storage, magnetic cassettes, magnetic tape magnetic disk storage or other magnetic storage devices or any other non-transmission media that can be used to store information that can be accessed by a computing device. As defined herein, computer readable media does not include temporary computer readable media (transitory media), such as modulated data signals and carrier waves.

[0170] It should also be noted that the terms "include", "comprises" or any other variations thereof are intended to cover non-exclusive inclusion, so that a process, method, commodity or device including a series of elements includes not only those elements, but also other elements not explicitly listed, or also includes elements inherent to such process, method, commodity or device. In the absence of more restrictions, the elements defined by the sentence "comprises a ..." do not exclude the existence of other identical elements in the process, method, commodity or device including the elements.

[0171] The above is only an embodiment of the present application and is not intended to limit the present application. For those skilled in the art, the present application may have various changes and variations. Any modification, equivalent replacement, improvement, etc. made within the spirit and principle of the present application should be included in the scope of the claims of the present application.

Claims

1. A method for determining a host physiological parameter, characterized in that: The method comprises: determining the impedance value of the host tissue fluid according to the test current and test voltage of the host physiological parameter detection device; Determining the current body temperature of the host based on the impedance value and a fitting function between the impedance value and the host body temperature; Based on the compensation function between the host body temperature and the host physiological parameter, the host physiological parameter corresponding to the current body temperature of the host is determined.

2. The determination method according to claim 1, characterized in that: Before determining the current body temperature of the host based on the impedance value and the fitting function between the impedance value and the host body temperature, the method further includes: Collecting a plurality of first currents and first voltages of a host physiological parameter detection device, and a plurality of corresponding first host body temperatures; determining an impedance value of host tissue fluid based on the first current and the first voltage, and determining a resistivity corresponding to the impedance value according to a mapping relationship between the impedance value and the resistivity; Based on the resistivity and the corresponding first host body temperature, a preliminary fitting function between the resistivity of the host tissue fluid and the host body temperature is determined, and the fitting function is determined in combination with the preliminary fitting function and the mapping relationship.

3. The method for determining a host physiological parameter according to claim 1, characterized in that: Determining the current body temperature of the host based on the impedance value and a fitting function between the impedance value and the host body temperature includes: Determining a ratio between a length and an average cross-sectional area of ​​a transmission path of the host physiological parameter detection device in the host tissue fluid; The current body temperature of the host is determined according to the impedance value, the ratio and the fitting function.

4. A method for determining a host physiological parameter according to claim 1, characterized in that: Determining the host physiological parameter corresponding to the current body temperature of the host based on a compensation function between the host body temperature and the host physiological parameter includes: Based on the corresponding relationship between the host body temperature and the compensation function, a matrix transformation is performed on the current body temperature of the host to obtain a transformed body temperature matrix; The host physiological parameters corresponding to the host's current body temperature are determined based on the compensation function, the body temperature matrix and the test voltage; or, the host physiological parameters corresponding to the host's current body temperature are determined based on the compensation function, the body temperature matrix and the test current.

5. The method for determining a host physiological parameter according to claim 1, characterized in that: The compensation function includes a first compensation function and a second compensation function. Before determining the host physiological parameter corresponding to the current body temperature of the host, the method further includes: determining the first compensation function based on a first relationship function among the test voltage, the host body temperature, and the host physiological parameter; or, The second compensation function is determined based on a second relationship function among the test current, the host body temperature, and the host physiological parameter.

6. A method for determining a host physiological parameter according to claim 5, characterized in that: Before determining the host physiological parameter corresponding to the current body temperature of the host, the method further includes: Acquiring reduction concentration information, reduction product coefficient and reducing agent coefficient of the host tissue fluid during the reaction; the reduction concentration information includes the reduction product concentration and the reducing agent concentration; Determining a first proportional coefficient and a second proportional coefficient according to the correlation between the reduction concentration information and the host physiological parameter, the reduction product coefficient, and the reducing agent coefficient; determining a difference between the reduction product coefficient and the reducing agent coefficient, and determining the first compensation function according to a ratio between the first proportional coefficient and the difference and a ratio between the second proportional coefficient and the difference; The second compensation function is determined according to the ratio between the length of the transmission path and the average cross-sectional area, the first relationship function, and the fitting function.

7. A method for determining a host physiological parameter according to claim 5, characterized in that: The first compensation function is: lnG=α0+α1ΔU+α2ΔU 2 +…+a n D.U. n ; The first relationship function is: Where G is the host physiological parameter; α0, α1, α2, ..., α n is the coefficient of the first compensation function; ΔU is the difference between the current test voltage and the initial test voltage of the electrode of the host physiological parameter detection device; R is the gas constant, n is the number of moles of electrons exchanged in the reaction, and F is the Faraday constant; C1 is the concentration of reduction products; C2 is the reducing agent concentration; a is the reduction product coefficient, b is the reducing agent coefficient, and T is the host body temperature.

8. A method for determining a host physiological parameter according to claim 5, characterized in that: The second compensation function is: lnG=β0+β1I test +β2I test 2 +…+b n I test n ; The second relationship function is: Where G is the host physiological parameter; β0, β1, β2, ..., β n I is the coefficient of the second compensation function; test A test current for a host physiological parameter detection device; R is the gas constant, n is the number of moles of electrons exchanged in the reaction, and F is the Faraday constant; C1 is the concentration of reduction products; C2 is the reducing agent concentration; a is the reduction product coefficient; b is the reducing agent coefficient; T is the host body temperature; L is the transmission path length; S is the average cross-sectional area of ​​the transmission path; A and B are the coefficients of the fitting function.

9. A device for determining a host physiological parameter, characterized in that: The device comprises: at least one processor; and, a memory communicatively coupled to the at least one processor; The memory stores instructions executable by the at least one processor, and the instructions are executed by the at least one processor so that the at least one processor can execute a method for determining a host physiological parameter as described in any one of claims 1-8.

10. A non-volatile computer storage medium storing computer executable instructions, characterized in that: The computer executable instructions are configured to: A method for determining a host physiological parameter as described in any one of claims 1 to 8.

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