Active level evaluation system and method based on flexible microfluidic sensor

Abstract

The invention provides an activity level evaluation system and method based on a flexible micro-fluidic sensor, the system comprises the flexible micro-fluidic sensor, an environment sensor, a power supply module, a signal conditioning circuit, a micro-control unit, a Bluetooth module and a display module, and the method comprises the following steps: preparing the flexible micro-fluidic sensor; and calibrating the flexible micro-fluidic sensor, assembling the activity level evaluation system based on the flexible micro-fluidic sensor, and evaluating the activity level. Human or animal physiological parameter data are obtained through an advanced flexible microfluidic sensing technology, environmental parameter data obtained by combining an environmental sensor are processed by a microcontroller to obtain a vitality level comprehensive value M, and a vitality level result is displayed, so that the convenience and comfort of detection are improved, and the detection accuracy is improved. And accurate evaluation of the activity level of human or animals is realized.

Description

Technical Field

[0001] The present invention relates to the field of flexible electronic technology, and in particular to a system and method for evaluating an activity level based on a flexible microfluidic sensor. Background Art

[0002] Vitality level assessment is not only the key to health management, but also an important means to improve overall social productivity and well-being. In the field of human or animal health, accurate assessment of individual vitality levels can help to detect potential health problems early, such as fatigue accumulation and decreased immunity, so as to take timely intervention measures to prevent the occurrence or deterioration of diseases. Traditional vitality assessment methods mostly rely on questionnaires, physiological index monitoring (such as heart rate, blood pressure), etc. Although these methods have certain effects, they often have problems such as strong subjectivity, poor real-time performance, and low comfort. The emergence of flexible microfluidic sensors has brought revolutionary changes to vitality assessment. Its flexible characteristics enable the sensor to fit closely to human skin, reduce discomfort, and improve wearing comfort. Microfluidic technology can precisely manipulate fluids on a microscale to achieve highly sensitive and highly selective biomolecule detection. Compared with traditional biochemical detection methods, flexible microfluidic sensors not only have higher flexibility and adaptability, but also can achieve non-invasive or minimally invasive detection, reducing interference and harm to patients or subjects. In addition, its integrated and portable design is also convenient for daily wear and remote monitoring, which lays the foundation for the vitality level in the blood of humans or animals.

[0003] Therefore, there is an urgent need for a vitality level assessment system and method based on flexible microfluidic sensors. The system can capture and analyze physiological parameters (blood glucose concentration and lactate concentration) and environmental parameters (temperature, humidity, oxygen, carbon dioxide) in real time. Combined with the method, efficient, accurate and comfortable vitality level assessment can be achieved, overcoming the limitations of traditional assessment methods and providing personalized health management recommendations for humans or animals. Summary of the invention

[0004] In order to overcome the deficiencies of the prior art, the object of the present invention is to provide a vitality level assessment system and method based on a flexible microfluidic sensor.

[0005] To achieve the above object, the present invention provides the following solutions:

[0006] The present invention provides a vitality level assessment system based on a flexible microfluidic sensor, comprising:

[0007] Flexible microfluidic sensor, environmental sensor, power module, signal conditioning circuit, microcontroller unit, Bluetooth module and display module, the power module is used for power supply, the flexible microfluidic sensor and environmental sensor are connected to the microcontroller unit through the signal conditioning circuit, which is used for transmitting physiological factor parameters and environmental factor parameters to the microcontroller unit, the microcontroller unit is used for evaluating vitality level according to the physiological factor parameters and environmental factor parameters, the microcontroller unit is connected to the display module and Bluetooth module, and the Bluetooth module is used for connecting to a mobile phone app.

[0008] Preferably, the flexible microfluidic sensor comprises, from top to bottom, a FHRP encapsulation layer, a dual-sensing electrode layer, a sensitive layer, a NPDM microfluidic layer, a first adhesive layer, a porous membrane and a second adhesive layer, the FHRP encapsulation layer is made of a modified material, the dual-sensing electrode layer is prepared by a template method, the sensitive layer is made of a blood glucose reagent and a lactic acid reagent, the NPDM microfluidic layer is made by temperature-controlled molding, the first adhesive layer and the second adhesive layer are double-sided tapes, and the porous membrane is made of a cellulose material.

[0009] The present invention also provides a method for evaluating vitality level based on a flexible microfluidic sensor, comprising:

[0010] Preparation of flexible microfluidic sensors;

[0011] Calibrate flexible microfluidic sensors;

[0012] Assemble a vitality level assessment system based on flexible microfluidic sensors and perform vitality level assessment.

[0013] Preferably, the flexible microfluidic sensor is prepared by:

[0014] Design and prepare the mold structure of NPDM microfluidic layer;

[0015] The NPDM microfluidic layer was prepared by temperature-controlled casting method;

[0016] The dual-sensing electrode was prepared by the template method;

[0017] Making a sensitive layer modified with blood glucose and lactate detection reagents;

[0018] A porous membrane is prepared using a mixed solution of cellulose and a hydrophilic agent;

[0019] The sensitive layer is placed in the NPDM microfluidic layer, and the dual sensing electrodes and the porous membrane are combined and encapsulated through the adhesive layer to make a flexible microfluidic sensor.

[0020] Preferably, the NPDM microfluidic layer is prepared by a temperature-controlled inverting molding method, specifically:

[0021] The main agent polydimethylsiloxane and the curing agent are mixed in a ratio of 10:1, and the curing agent is one of peroxide or silane coupling agent. The FHRP prepolymer, cross-linking agent, reinforcing material and hybrid material are mixed in a certain proportion. The mixed reagents are stirred in a beaker for 25 minutes at a speed of 200 rpm, and excess bubbles are removed by ultrasound. The mixed reagents are poured into the prepared polytetrafluoroethylene NPDM microfluidic layer mold, and the mold is placed in a drying oven at 45°C and dried for 12 hours. After curing, it is demolded from the mold to prepare the NPDM microfluidic layer.

[0022] Preferably, the dual sensing electrode is prepared by a template method, specifically:

[0023] A silicon carbide template with regular pores is prepared, and graphene is grown on the template. After the growth is completed, the template is removed by chemical corrosion or physical stripping to expose the surface of the dual-sensing electrode. After removing the template, the graphene is cut and formed to meet the specific size and shape requirements of the electrode, and post-processed cleaning, drying and annealing are performed.

[0024] Preferably, the sensitive layer modified with blood glucose and lactate detection reagents is prepared as follows:

[0025] Select a test paper of appropriate size and a reagent for detecting the biomarker to be tested, evenly apply the reagent on the test paper, dry the applied test paper, and cut the dried test paper into a square with a side length of 5θmm according to the size of the reaction chamber to make a sensitive layer suitable for a flexible microfluidic sensor. The overall size can be scaled according to a certain proportional factor θ to meet the specific needs of different occasions.

[0026] Preferably, the porous membrane is prepared using a mixed solution of cellulose and a hydrophilic agent, specifically:

[0027] The treated cellulose solution is mixed and stirred with the hydrophilic reagent, and poured evenly onto a flat substrate. The thickness of the coating is controlled by a scraper, and the solvent is allowed to evaporate naturally or accelerated by heating to form a porous membrane.

[0028] Preferably, the flexible microfluidic sensor is calibrated by:

[0029] Collect sweat and blood containing blood sugar and lactic acid from humans or animals at different time periods, use the prepared flexible microfluidic sensor to detect the sweat, and then use an electrochemical workstation to collect the current changes of the flexible microfluidic sensor;

[0030] The collected blood was tested using a standard blood glucose tester and a lactate tester to obtain the blood glucose concentration and lactate concentration, and a relationship between the electrical signal of the flexible microfluidic sensor and the blood glucose concentration and lactate concentration was established.

[0031] Preferably, an activity level assessment is performed, specifically:

[0032] Flexible microfluidic sensors are used to precisely control the fluid to detect physiological factor parameters, namely blood glucose concentration and lactate concentration. Combined with environmental factor parameters obtained by environmental sensors, namely temperature, humidity, oxygen, and carbon dioxide data, the microcontroller processes to obtain a comprehensive value M of vitality level and displays the vitality level results.

[0033] Construct R d The time series set T of the dimensional feature data contains four signals, namely temperature, humidity, oxygen and carbon dioxide. The calculation formula for the cumulative amount ΔA of each parameter variable during the calculation time period is:

[0034]

[0035] In the formula, A T represents the characteristic function of each signal, represents the change in the average value of each signal during the acquired time period, and the weight γ ij It was determined based on the correlation coefficient between each parameter and vitality, and its absolute value was directly used as the weight value;

[0036] Calculate the vitality index accumulated from the environmental factors of temperature, humidity, oxygen and carbon dioxide for:

[0037]

[0038] In the formula, τ ij Stress correction coefficients representing the environmental factor parameters for each organism;

[0039] Based on the extracted blood glucose concentration and lactate concentration characteristic parameters, the collected data are processed to obtain the morphological characteristic parameter k. Based on the morphological characteristic parameter k, the vitality level classification rule is established, and the blood glucose concentration sample group and the lactate concentration sample group are integrated to obtain the cumulative vitality level. for:

[0040]

[0041] The vitality level is affected by physiological factors and environmental factors. The final vitality level M is:

[0042]

[0043] In the formula, It is the vitality index accumulated from environmental factor parameters. is the vitality index obtained by accumulating physiological factor parameters, M is the final vitality level, and the weight μ iDetermined by the correlation coefficient between physiological factor parameters and environmental factor parameters and vitality level, where μ C =0.382, μ D =0.618.

[0044] According to the specific embodiments provided by the present invention, the present invention discloses the following technical effects:

[0045] The present invention provides a system and method for evaluating vitality level based on a flexible microfluidic sensor, and the beneficial effects are as follows:

[0046] (1) The present invention uses FHRP material formed by hybrid enhancement by adding other materials, and the conductivity and stability of the flexible microfluidic sensor prepared by the material are greatly improved;

[0047] (2) The flexible microfluidic sensor is small in size and has good flexibility. Through the specially structured NPDM microfluidic layer, the flow and mixing of the fluid can be precisely controlled, thereby enabling the detection of tiny signals.

[0048] (3) The present invention provides a calibration method for a flexible microfluidic sensor, which is based on the electrochemical detection of sweat by the flexible microfluidic sensor, and the detection of the collected blood by a standard detector. Through data analysis, the relationship between the electrical signal of the flexible microfluidic sensor and the physiological parameters (blood glucose concentration and lactate concentration) is obtained, namely, the calibration formulas of "flexible microfluidic blood glucose sensor signal-blood glucose concentration" and "flexible microfluidic lactate sensor signal-lactic acid concentration" are obtained;

[0049] (4) The present invention accurately reflects the blood glucose concentration and lactate concentration based on the established "flexible microfluidic blood glucose sensor signal-blood glucose concentration" and "flexible microfluidic lactate sensor signal-lactic acid concentration" calibration formulas, and combines the environmental parameters (temperature, humidity, oxygen, carbon dioxide) data obtained by the environmental sensor to obtain the comprehensive value M of the vitality level, thereby further realizing the non-destructive evaluation of the vitality level of humans or animals. Similarly, this flexible microfluidic sensor can be applied to the non-destructive detection of more biomarkers, providing effective protection for the physiological health of humans or animals. BRIEF DESCRIPTION OF THE DRAWINGS

[0050] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings required for use in the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying creative labor.

[0051] Figure 1 A schematic diagram of the structure of a flexible microfluidic sensor provided by an embodiment of the present invention;

[0052] Figure 2 A mold structure diagram of the NPDM microfluidic layer provided in an embodiment of the present invention;

[0053] Figure 3 A structural diagram of the NPDM microfluidic layer provided in an embodiment of the present invention;

[0054] Figure 4 A diagram showing the preparation of an OR-MX loaded dual-sensing electrode provided in an embodiment of the present invention;

[0055] Figure 5 A schematic diagram of the blood sugar response detection principle provided by an embodiment of the present invention;

[0056] Figure 6 A schematic diagram of the lactic acid reaction detection principle provided by an embodiment of the present invention;

[0057] Figure 7 A hardware structure diagram of a human or animal vitality assessment provided by an embodiment of the present invention;

[0058] Figure 8 A human or animal vitality assessment framework diagram provided by an embodiment of the present invention;

[0059] Fig. 9 A schematic flow chart of a method for evaluating activity levels based on a flexible microfluidic sensor provided in an embodiment of the present invention. DETAILED DESCRIPTION

[0060] The following will be combined with the drawings in the embodiments of the present invention to clearly and completely describe the technical solutions in the embodiments of the present invention. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present invention.

[0061] In order to make the above-mentioned objects, features and advantages of the present invention more obvious and easy to understand, the present invention is further described in detail below with reference to the accompanying drawings and specific embodiments.

[0062] Figure 7 A schematic diagram of the system structure provided by an embodiment of the present invention, such as Figure 7As shown, the present invention provides a vitality level assessment system based on a flexible microfluidic sensor, comprising: a flexible microfluidic sensor, an environmental sensor, a power module, a signal conditioning circuit, a microcontroller unit, a Bluetooth module and a display module, wherein the power module is used for supplying power, the flexible microfluidic sensor and the environmental sensor are connected to the microcontroller unit through the signal conditioning circuit for transmitting physiological factor parameters and environmental factor parameters to the microcontroller unit, the microcontroller unit is used for performing vitality level assessment according to the physiological factor parameters and the environmental factor parameters, the microcontroller unit is connected to the display module and the Bluetooth module, and the Bluetooth module is used for connecting to a mobile phone app.

[0063] The flexible microfluidic sensor comprises, from top to bottom, a FHRP encapsulation layer, a dual-sensing electrode layer, a sensitive layer, a NPDM microfluidic layer, a first adhesive layer, a porous membrane and a second adhesive layer. The FHRP encapsulation layer is made of a modified material, the dual-sensing electrode layer is prepared by a template method, the sensitive layer is made of a blood glucose reagent and a lactic acid reagent, for example, glucose oxidase (GOD) and lactate oxidase (LOx), the NPDM microfluidic layer is made by temperature-controlled molding, the first adhesive layer and the second adhesive layer are double-sided adhesives, and the porous membrane is made of a cellulose material.

[0064] like Fig. 9 As shown, the present invention also provides a method for evaluating vitality level based on a flexible microfluidic sensor, which is characterized by comprising:

[0065] Step 100: preparing a flexible microfluidic sensor;

[0066] Step 200: calibrating the flexible microfluidic sensor;

[0067] Step 300: Assemble a vitality level assessment system based on a flexible microfluidic sensor and perform vitality level assessment.

[0068] In step 100, a flexible microfluidic sensor is prepared, specifically:

[0069] The choice of materials will directly affect the performance of flexible microfluidic sensors. The materials available for flexible packaging include polyvinyl alcohol, polyethylene naphthalate, polyester, or quartz, silicon, or paper. The present invention uses FHRP material after hybrid enhancement, which has the advantages of good flexibility, high light transmittance, strong corrosion resistance, etc.; the electrode layer is made by a template method to form graphene, and has the advantages of high stability, repeatability, and structural controllability; the microfluidic layer made by the temperature-controlled inverted molding method has outstanding advantages such as high resolution and flexibility, repeatability and easy manufacturing, good sealing, applicability to a variety of materials, and compatibility with other technologies.

[0070] Based on advanced flexible material technology, a structure combining microfluidics and sensing electrodes is designed to achieve fast and accurate capture of biomolecules. Based on electrochemical principles, the electrochemical signals generated can be directly correlated to physiological parameters (blood sugar concentration and lactate concentration).

[0071] The detection of blood sugar concentration and lactic acid concentration is based on the corresponding reagents. For blood sugar detection: fix glucose oxidase on the sensitive layer to form a polymer film. For lactic acid detection: fix lactate oxidase on the sensitive layer and evenly apply it on a test paper of appropriate size.

[0072] During the manufacturing process of the electrode layer, OR-MX with high conductivity and oxidation resistance is loaded onto the working electrode. The sensor made by the scheme has high sensitivity and good flexibility, which makes it possible to detect physiological parameters (blood sugar concentration and lactate concentration) in real time and continuously. This invention provides important technical support for the field of physiological health, especially in sports physiology, intensive care and chronic disease management. The specific production steps are as follows:

[0073] Step 101: designing and preparing a mold structure of a NPDM microfluidic layer;

[0074] Step 102: preparing the NPDM microfluidic layer by using a temperature-controlled inverting molding method;

[0075] Step 103: preparing a dual-sensing electrode by a template method;

[0076] Step 104: preparing a sensitive layer modified with blood glucose and lactate detection reagents;

[0077] Step 105: preparing a porous membrane using a mixed solution of cellulose and a hydrophilic agent;

[0078] Step 106: Place the sensitive layer into the NPDM microfluidic layer, combine and encapsulate the dual sensing electrodes and the porous membrane through an adhesive layer to make a flexible microfluidic sensor.

[0079] In step 101, a mold structure (such as Figure 2 ), specifically:

[0080] The mold base is 40θmm*40θmm*1.5θmm and is made of polytetrafluoroethylene (PTFE). A fence with an inner diameter of 30θmm*30θmm and an outer diameter of 40θmm*40θmm is added to the mold base. A protruding pattern is set on the inner platform of the fence on the mold base. The protruding pattern includes a non-circular protrusion with an aperture of 5θmm and a height of 1.5θmm, and two square protrusions with a side length of 5θmm*5θmm*0.7θmm. In addition, there are two linear channels connecting the sweat collection hole and the reaction chamber, and then communicating with the atmosphere. The channel width is 0.8θmm and the depth is 0.7θmm. The overall size can be scaled according to a certain proportional factor θ to meet the specific needs of different occasions.

[0081] In step 102, the NPDM microfluidic layer is prepared by a temperature-controlled inverting molding method, specifically:

[0082] To prepare the NPDM microfluidic layer, mix the main agent FHRP and the curing agent in a ratio of 10:1. The curing agent may be a peroxide or a silane coupling agent. The main purpose is that they can react with the functional groups in the FHRP polymer to crosslink and cure the polymer chains. Stir the mixed reagents in a beaker for 25 minutes at a speed of 200 rpm, then use ultrasound to remove excess bubbles, and finally pour the mixed reagents into the prepared polytetrafluoroethylene (PTFE) mold, put the mold into a drying oven at 45°C and dry it for 12 hours, and finally demold the cured FHRP from the mold to prepare the NPDM microfluidic layer with the designed grooved channels. Figure 3 As shown, the overall size of the NPDM microfluidic layer is 30θmm*30θmm*1.5θmm, and the FHRP microfluidic flow channel layer base membrane includes a non-circular groove with a diameter of 5θmm and a depth of 1.5θmm, i.e., the sweat collection hole; there are also two square grooves with a side length of 7θmm and a depth of 0.7θmm, and the square grooves are pre-stored with test papers modified with detection reagents, i.e., reaction chambers; there is also a liquid channel connecting the sweat collection hole and the reaction chamber, and the flow channel is 0.8θmm wide and 0.7θmm deep, and then communicates with the atmosphere.

[0083] In step 103, a dual-sensing electrode is prepared by a template method, specifically:

[0084] First, a silicon carbide template with regular pores is prepared to ensure that the pores of the template have the required shape and size. Next, graphene is grown on the template, which involves methods such as chemical vapor deposition, in which the carbon source decomposes at high temperature and forms graphene in the pores of the template. Parameters such as temperature, atmosphere and pressure need to be precisely controlled to ensure the quality and uniformity of graphene. After the graphene growth is completed, the template is removed by chemical corrosion or physical stripping to expose the surface of the dual-sensing electrode. After removing the template, the graphene is cut and formed to meet the specific size and shape requirements of the electrode. Post-processing cleaning, drying and annealing are then carried out to improve the performance and stability of the electrode. Subsequently, FHRP elastomer is spin-coated on the electrode at a speed of 1200r / min for a duration of about 8s and cured at 80°C for 100min to ensure that the electrode is stably attached to FHRP. The reference electrode is coated with Ag / AgCl paste by printing technology, then dried in an oven at 15 minutes and placed in an oven at 120°C for 15 minutes. Finally, OR-MX was deposited on the working electrode, where the OR-MX material was prepared by adding inorganic polyanion salts to the MXene colloidal suspension to slow down the oxidation process, and then dried for 6 hours. Figure 4 shown.

[0085] In step 104, a sensitive layer modified with blood glucose and lactate detection reagents is prepared, specifically:

[0086] Select a suitable reagent and apply it on the test paper, dry it so that the reagent can be better fixed on the test paper, and then cut the dried test paper into a size that matches the reaction chamber, thereby making a test paper suitable for use in a flexible microfluidic sensor.

[0087] Blood sugar detection: Glucose oxidase is fixed on the sensitive layer to form a polymer film. Under the catalytic action of glucose oxidase, glucose in sweat is oxidized by O2 into gluconolactone and H2O2. Lactic acid detection: Lactate oxidase is fixed on the sensitive layer and evenly applied to a test paper of appropriate size. The reaction process is mainly divided into two steps. The speed of generating brown-red substances in the second step is relatively slow. The reaction detection principle of blood sugar and lactic acid is as follows: Figure 5 and Figure 6 shown.

[0088] In step 105, a porous membrane is prepared using a mixed solution of cellulose and a hydrophilic agent, specifically:

[0089] The treated cellulose solution is mixed and stirred with the hydrophilic reagent, and poured evenly onto a flat substrate. The thickness of the coating is controlled by a scraper or other tool, and then the solvent is allowed to evaporate naturally or dried faster by heating to form a porous membrane, thereby achieving the purpose of accelerating the absorption rate of sweat and filtering out impurities in sweat during testing.

[0090] In step 106, the sensitive layer is placed in the NPDM microfluidic layer, and the dual sensing electrodes and the porous membrane are combined and packaged through an adhesive layer to make a flexible microfluidic sensor, specifically:

[0091] The adhesive layer is a double-sided medical tape with a size of 3θcm*3θcm, and a circular hole with a diameter of 5θmm is made in the center of the tape using a hole puncher. The adhesive layer is then used to align and paste the NPDM microfluidic layer, dual-sensing electrodes, porous membrane, and FHRP encapsulation layer that have been placed in the sensitive layer to ensure that the circular hole is precisely docked with the sweat collection hole to form an efficient and stable flexible microfluidic sensor. When using it, if the sample is directly injected, the tape can be facing up, or the tape can be omitted; if it is used on the skin, one side of the tape is adhered to the FHRP membrane and the other side is adhered to the skin surface.

[0092] In step 200, the flexible microfluidic sensor is calibrated, specifically:

[0093] The flexible microfluidic sensor is used to detect human or animal sweat, and an electrical signal related to blood glucose concentration and lactate concentration is obtained by an electrochemical workstation, and a relationship between the electrical signal of the flexible microfluidic sensor and the blood glucose concentration and lactate concentration is established. The specific steps are as follows:

[0094] Step 201: collect sweat and blood containing blood sugar and lactic acid from humans or animals at different time periods, use the prepared flexible microfluidic sensor to detect the sweat, and then collect the current change of the flexible microfluidic sensor through an electrochemical workstation, specifically:

[0095] First, the performance of the flexible microfluidic sensor described above is tested (including accuracy, response time, stability, linearity and sensitivity, etc.) to ensure stable and reliable performance. Next, the flexible microfluidic sensor is used to detect the collected human or animal sweat, and the current change of the flexible microfluidic sensor is collected by an electrochemical workstation;

[0096] Step 202: Use a standard blood glucose detector and a lactate detector to detect the collected blood to obtain the blood glucose concentration and the lactate concentration, and establish a relationship between the electrical signal of the flexible microfluidic sensor and the blood glucose concentration and the lactate concentration, specifically:

[0097] Use a standard blood glucose detector and lactate detector to test the blood glucose and lactate in humans or animals to obtain the blood glucose concentration and lactate concentration. Through data analysis, a relationship between the electrical signal of a flexible microfluidic sensor and physiological parameters (blood glucose concentration and lactate concentration) is constructed, namely, the "flexible microfluidic blood glucose sensor signal-blood glucose concentration" and "flexible microfluidic lactate sensor signal-lactic acid concentration" calibration formula;

[0098] Specifically, the prepared flexible microfluidic sensor was used to detect sweat containing n different blood glucose concentrations and lactate concentrations at room temperature, where C m Indicates the mth concentration value, C o Indicates that it does not contain blood glucose and lactate control solution; I m Indicates the current stability value corresponding to the mth concentration value, I o It indicates the stable current value corresponding to the control solution without blood sugar and lactate; A is a constant; ε is the random error; I mn Indicates the current stability value of the nth test corresponding to the mth concentration, ΔI m Indicates the current change value. The specific formula is as follows:

[0099]

[0100] In summary, the calibration formulas of "flexible microfluidic blood glucose sensor signal-blood glucose concentration" and "flexible microfluidic lactate sensor signal-lactic acid concentration" are obtained. The specific formulas are as follows:

[0101]

[0102] In step 300, a vitality level assessment system based on a flexible microfluidic sensor is assembled and vitality level assessment is performed, specifically:

[0103] Step 301: The flexible microfluidic sensor accurately controls the fluid to detect physiological factor parameters, namely, blood glucose concentration and lactate concentration, and combines the environmental factor parameters obtained by the environmental sensor, namely, temperature, humidity, oxygen, and carbon dioxide data, and the microcontroller processes to obtain a comprehensive value M of the vitality level and displays the vitality level result;

[0104] Step 302: Construct R d The time series set T of the dimensional feature data contains four signals, namely temperature, humidity, oxygen and carbon dioxide. The calculation formula for the cumulative amount ΔA of each parameter variable during the calculation time period is:

[0105]

[0106] In the formula, A T represents the characteristic function of each signal, represents the change in the average value of each signal during the acquired time period, and the weight γij It was determined based on the correlation coefficient between each parameter and vitality, and its absolute value was directly used as the weight value;

[0107] Calculate the vitality index accumulated from the environmental factors of temperature, humidity, oxygen and carbon dioxide for:

[0108]

[0109] In the formula, τ ij Stress correction coefficients representing the environmental factor parameters for each organism;

[0110] Step 303: construct the blood glucose concentration and lactate concentration characteristic signal sample matrix S and its mapping functions h(x) and h(y). The purpose of this step is to provide concentration samples for subsequent data F processing, where f c and f l They represent blood glucose concentration data samples and lactate concentration data samples respectively;

[0111]

[0112] Based on the extracted characteristic parameters of blood glucose concentration and lactate concentration, the collected data were processed to obtain a morphological characteristic parameter, denoted as "k". A vitality level classification rule was established based on this parameter k. The blood glucose concentration sample group and the lactate concentration sample group were then integrated to further characterize the cumulative vitality level, denoted as for:

[0113]

[0114] Step 304: Weighting the physiological parameters (blood sugar concentration and lactate concentration) and environmental parameters (temperature, humidity, oxygen, carbon dioxide) to obtain a comprehensive vitality value M, thereby further evaluating the vitality level. The vitality level is affected by the physiological factor parameters and the environmental factor parameters. The final vitality level M obtained by comprehensive consideration is:

[0115]

[0116] In the formula, It is the vitality index accumulated from environmental factor parameters. is the vitality index obtained by accumulating physiological factor parameters, M is the final vitality level, and the weight μ i Determined by the correlation coefficient between physiological factor parameters and environmental factor parameters and vitality level, where μ C =0.382, μ D =0.618.

[0117] The present invention provides an embodiment, designs a field test scheme for experimental subjects, fits a flexible microfluidic sensor to the target skin area, places it in an experimental environment, accurately detects the physiological parameters (blood sugar concentration and lactate concentration) in sweat, and combines the environmental parameters (temperature, humidity, oxygen, carbon dioxide) data obtained by the environmental sensor to obtain a comprehensive value of the vitality level, thereby evaluating the vitality of humans or animals. Based on cutting-edge literature and consulting relevant staff, the comparison of vitality level evaluation for humans, sheep and dogs as shown in Table 1 is obtained, thereby providing strong support for health monitoring and disease early warning. The framework diagram of vitality evaluation for humans or animals is shown in the figure below: Figure 8 shown.

[0118] Table 1 Comparison of vitality level assessment in humans, sheep and dogs

[0119]

[0120] The present invention also provides an embodiment, specifically: 10 healthy sheep with an average weight of (25±0.5) kg are randomly selected and reasonable grazing activities are carried out. Three prepared flexible microfluidic sensors are attached to the neck of each test sheep to detect sweat. The acquired data are processed to obtain M1, M2, and M3, and the comprehensive value M of the vitality level is obtained by calculation. According to Table 1, the vitality level of the sheep can be obtained as lethargic, normal, or stressed, and the value is wirelessly transmitted to the intelligent port through the Bluetooth communication module.

[0121]

[0122] Ten healthy people were selected as test participants, with a height of 170 cm, a weight of (65±0.5) kg, and an age of 25 years. A 24-h training plan (including rest and practice) was arranged reasonably. Three prepared flexible microfluidic sensors were attached to the arms of each participant to detect sweat to evaluate the participant's vitality level. The acquired data were processed to obtain M1, M2, and M3, and the comprehensive vitality level M was calculated. According to Table 1, the participant's vitality level, fatigue, normal, or excitement, can be obtained, and the value is wirelessly transmitted to the smart port through the Bluetooth communication module.

[0123]

[0124] Ten healthy dogs were randomly selected with an average weight of (15±0.3) kg and performed moderate daily activities. Each dog wore three prepared flexible microfluidic sensors around its nose for real-time detection of sweat to assess the dog's vitality level. The acquired data was processed to obtain M1, M2, and M3, and the comprehensive value of vitality level M was calculated. According to Table 1, the dog's vitality level can be obtained as weak, normal, or active, which is wirelessly transmitted to the smart port through the Bluetooth communication module.

[0125]

[0126] The various embodiments in this specification are described in a progressive manner, and each embodiment focuses on the differences from other embodiments. The same or similar parts between the various embodiments can be referenced to each other.

[0127] The principles and implementation methods of the present invention are described in this article using specific examples. The description of the above embodiments is only used to help understand the method and core idea of ​​the present invention. At the same time, for those skilled in the art, according to the idea of ​​the present invention, there will be changes in the specific implementation methods and application scope. In summary, the content of this specification should not be understood as limiting the present invention.

Claims

1. A vitality level assessment system based on a flexible microfluidic sensor, characterized in that: include: Flexible microfluidic sensor, environmental sensor, power module, signal conditioning circuit, microcontroller unit, Bluetooth module and display module, the power module is used for power supply, the flexible microfluidic sensor and environmental sensor are connected to the microcontroller unit through the signal conditioning circuit, which is used for transmitting physiological factor parameters and environmental factor parameters to the microcontroller unit, the microcontroller unit is used for evaluating vitality level according to the physiological factor parameters and environmental factor parameters, the microcontroller unit is connected to the display module and Bluetooth module, and the Bluetooth module is used for connecting to a mobile phone app.

2. The system according to claim 1, characterized in that The structure of the flexible microfluidic sensor is, from top to bottom, a FHRP encapsulation layer, a dual-sensing electrode layer, a sensitive layer, a NPDM microfluidic layer, a first adhesive layer, a porous membrane and a second adhesive layer. The FHRP encapsulation layer is made of a modified material, the dual-sensing electrode layer is prepared by a template method, the sensitive layer is made of a blood glucose reagent and a lactic acid reagent, the NPDM microfluidic layer is made by temperature-controlled molding, the first adhesive layer and the second adhesive layer are double-sided tapes, and the porous membrane is made of a cellulose material.

3. A method for evaluating vitality level based on a flexible microfluidic sensor, characterized in that: include: Preparation of flexible microfluidic sensors; Calibrate flexible microfluidic sensors; Assemble a vitality level assessment system based on flexible microfluidic sensors and perform vitality level assessment.

4. The method according to claim 3, characterized in that: Prepare a flexible microfluidic sensor, specifically: Design and prepare the mold structure of NPDM microfluidic layer; The NPDM microfluidic layer was prepared by temperature-controlled casting method; The dual-sensing electrode was prepared by the template method; Making a sensitive layer modified with blood glucose and lactate detection reagents; A porous membrane is prepared using a mixed solution of cellulose and a hydrophilic agent; The sensitive layer is placed in the NPDM microfluidic layer, and the dual sensing electrodes and the porous membrane are combined and encapsulated through the adhesive layer to make a flexible microfluidic sensor.

5. The method according to claim 4, characterized in that The NPDM microfluidic layer was prepared by temperature-controlled inverting molding method, specifically: The main agent polydimethylsiloxane and the curing agent are mixed in a ratio of 10:1, and the curing agent is one of peroxide or silane coupling agent. The FHRP prepolymer, cross-linking agent, reinforcing material and hybrid material are mixed in a certain proportion. The mixed reagents are stirred in a beaker for 25 minutes at a speed of 200 rpm, and excess bubbles are removed by ultrasound. The mixed reagents are poured into the prepared polytetrafluoroethylene NPDM microfluidic layer mold, and the mold is placed in a drying oven at 45°C and dried for 12 hours. After curing, it is demolded from the mold to prepare the NPDM microfluidic layer.

6. The method according to claim 4, characterized in that The dual-sensing electrode was prepared by the template method, specifically: A silicon carbide template with regular pores is prepared, and graphene is grown on the template. After the growth is completed, the template is removed by chemical corrosion or physical stripping to expose the surface of the dual-sensing electrode. After removing the template, the graphene is cut and formed to meet the specific size and shape requirements of the electrode, and post-processed cleaning, drying and annealing are performed.

7. The method according to claim 4, characterized in that The sensitive layer modified with blood glucose and lactate detection reagents is prepared as follows: Select a test paper of appropriate size and a reagent for detecting the biomarker to be tested, evenly apply the reagent on the test paper, dry the applied test paper, and cut the dried test paper into a square with a side length of 5θmm according to the size of the reaction chamber to make a sensitive layer suitable for a flexible microfluidic sensor. The overall size can be scaled according to a certain proportional factor θ to meet the specific needs of different occasions.

8. The method according to claim 4, characterized in that A porous membrane is prepared using a mixed solution of cellulose and a hydrophilic reagent, specifically: The treated cellulose solution is mixed and stirred with the hydrophilic reagent, and poured evenly onto a flat substrate. The thickness of the coating is controlled by a scraper, and the solvent is allowed to evaporate naturally or accelerated by heating to form a porous membrane.

9. The method according to claim 3, characterized in that: The flexible microfluidic sensor is calibrated as follows: Collect sweat and blood containing blood sugar and lactic acid from humans or animals at different time periods, use the prepared flexible microfluidic sensor to detect the sweat, and then use an electrochemical workstation to collect the current changes of the flexible microfluidic sensor; The collected blood was tested using a standard blood glucose tester and a lactate tester to obtain the blood glucose concentration and lactate concentration, and a relationship between the electrical signal of the flexible microfluidic sensor and the blood glucose concentration and lactate concentration was established.

10. The method according to claim 3, characterized in that: Conduct an energy level assessment, specifically: Flexible microfluidic sensors are used to precisely control the fluid to detect physiological factor parameters, namely blood glucose concentration and lactate concentration. Combined with environmental factor parameters obtained by environmental sensors, namely temperature, humidity, oxygen, and carbon dioxide data, the microcontroller processes to obtain a comprehensive value M of vitality level and displays the vitality level results. Construct R d The time series set T of the dimensional feature data contains four signals, namely temperature, humidity, oxygen and carbon dioxide. The calculation formula for the cumulative amount ΔA of each parameter variable during the calculation time period is: In the formula, A T represents the characteristic function of each signal, represents the change in the average value of each signal during the acquired time period, and the weight γ ij It was determined based on the correlation coefficient between each parameter and vitality, and its absolute value was directly used as the weight value; Calculate the vitality index accumulated from the environmental factors of temperature, humidity, oxygen and carbon dioxide for: In the formula, τ ij Stress correction coefficients representing the environmental factor parameters for each organism; Based on the extracted blood glucose concentration and lactate concentration characteristic parameters, the collected data are processed to obtain the morphological characteristic parameter k. Based on the morphological characteristic parameter k, the vitality level classification rule is established, and the blood glucose concentration sample group and the lactate concentration sample group are integrated to obtain the cumulative vitality level. for: The vitality level is affected by physiological factors and environmental factors. The final vitality level M is: In the formula, It is the vitality index accumulated from environmental factor parameters. is the vitality index accumulated from the physiological factor parameters, M is the final vitality level, and the weight μi is determined according to the correlation coefficient between the physiological factor parameters and the environmental factor parameters and the vitality level, where μC = 0.382, μ D =0.618.

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