Body fluid detection device and detection method

Abstract

The present invention relates to a method and a device for detecting body fluids. The method for detecting body fluids includes the following steps: obtaining a body fluid sample; detecting the body fluid sample and generating the first detection signal; the first detection signal is used to generate a biometric value; wherein, the biometric value includes at least one of the excretion rate, excretion volume, and fatigue value of the body fluid. The method and device for detecting body fluids according to the present invention can respectively detect a body fluid sample to obtain a first detection signal, and can calculate a physical sign value through the first detection signal. The physical sign value can include the body fluid excretion rate, body fluid excretion volume, water balance, degree of hydration, and fatigue value, etc., which is convenient for users and medical staff to monitor the degree of body fluid loss in the human body and supplement body fluids when the body fluid loss is excessive.

Description

Technical Field

[0001] The present invention relates to the field of biological detection, and in particular, to a body fluid detection device and a sweat detection method. Background Art

[0002] Both wearable devices and the Internet of Things have been market hotspots in recent years, providing a basis for non-invasive detection. In the fields of health care devices, sports devices, etc., wearable devices can be used to non-invasively detect human-related data and send it to various personal terminals or medical centers, enabling autonomous and continuous collection and detection without the intervention of experts. This allows the wearer himself and medical staff, etc., to understand the wearer's physical condition in real time and in full.

[0003] Body fluids such as sweat, saliva, and tears can be obtained non-invasively, so the physical health of the human body can be identified by monitoring body fluids. Wearable body fluid sensors can collect and analyze body fluids. For applications involving dynamic physiological changes including sports, wearable sensors can provide instant measurement information so that individuals or medical staff can understand the health status of the tested person in a shorter time.

[0004] Taking sweat as an example, the most abundant ions in sweat are Na+ (sodium ion) and Cl- (chloride ion), which are responsible for the generation of sweat. Na+ and Cl- migrate back and forth between the blood and the secretory glands, thereby generating an osmotic pressure difference that forces water into the sweat glands. When sweat flows through the dermal ducts, Na+ and Cl- are reabsorbed through the channels in the dermal duct wall. The reabsorption rate of Na+ and Cl- in the dermal ducts is quite stable, resulting in the fact that Na+ and Cl- in the final sweat usually increase with the increase in the sweating rate.

[0005] Sweat lost through the skin has two forms: one is insensible perspiration, where about 500 ml of water is evaporated daily, and Na+ and Cl- are reabsorbed through the channels in the dermal duct wall, making the nature of insensible perspiration pure water basically free of electrolytes; the other is the sweat secreted by the sweat glands, and its excretion amount is related to the temperature, humidity, labor intensity (or exercise intensity) of the external environment or the physical health of the human body. For example, when the temperature reaches 28°C, the sweat glands start to secrete sweat. The composition of the sweat is similar to that of urine, but it is very dilute. Compared with plasma, it is hypotonic. The concentration of NaCl (sodium chloride) in sweat is about 0.2%, which is about 1 / 5 to 1 / 2 of that in plasma. Sweat also contains a small amount of K+ (potassium ion) (about 5 - 10 mmol / L), Ca2+ (calcium ion), and 10 free amino acids, etc. In addition, when the human body experiences acute pain, the sweat glands will also secrete a large amount of sweat in a short time. In some eye diseases, the eyes will keep shedding tears; or in digestive diseases, saliva will also flow out of the mouth in a large amount in a short time.

[0006] Sweat, as a non-invasive body fluid sample, has the potential to be used as an indicator for health management. Sweat is mainly secreted by exocrine glands. The eccrine sweat gland consists of a secretory coil, which is the origin of sweat. Sweat is transported from the dermal duct through the epidermis to the skin surface. During this process, various analytes, including ions, metabolites, amino acids, hormones, proteins, and polypeptides, are excreted from the nearby blood and tissue fluid into the sweat and then discharged out of the body; these biomolecules and chemical elements carry a large amount of human health information and have great value for exploration. A review article on sweat published in Nature in 235 listed nearly 20 biomarker information in sweat and their detection methods. In addition to detecting the biomarker information in sweat, the sweat flow rate (sweat excretion rate) within a predetermined time can also be used as a standard human health indicator. For example, the energy loss and exercise fatigue of a person can be detected by measuring the sweating rate.

[0007] During exercise, wearable devices such as sports bracelets usually detect heart rate and cannot detect sweat. Most of the existing sweat detection equipment uses colorimetry to detect the presence of biomarker information such as Na+, Cl-, pH, glucose, and lactate in sweat, so as to determine whether the sweat is insensible sweat or sweat secreted by sweat glands. It is impossible to detect the sweat excretion rate, and thus impossible to detect and analyze the body fluid excretion rate, excretion volume, and exercise fatigue value of a person. Summary of the Invention

[0008] In view of this, the present invention provides a body fluid detection device that can obtain physical signs such as body fluid excretion rate, excretion volume, and fatigue value by detecting a body fluid sample, and a detection method for the body fluid detection device.

[0009] The above technical problems are solved by adopting the following technical solutions:

[0010] The present invention provides a body fluid detection method, including the following steps:

[0011] Obtain a body fluid sample;

[0012] Detect the body fluid sample and generate the first detection signal; wherein, multiple detection points are included to detect the body fluid sample;

[0013] The first detection signal is used to generate physical sign values; wherein, the physical sign values include at least one of the excretion rate, excretion volume, and fatigue value of the body fluid.

[0014] Preferably, the process of detecting the body fluid sample and generating the first detection signal includes the following steps:

[0015] Detect a body fluid sample through at least one sensor, and switch between a first state and a second state of at least one of the sensors;

[0016] The body fluid sample sequentially passes through the detection points along a predetermined order, and is electrically connected to the corresponding sensors at each detection point;

[0017] Switching between the first state and the second state of the sensor in contact with the body fluid sample;

[0018] According to the switching time of the first state and the second state of each of the sensors, the sampling circuit generates one or more first detection signals, or according to the combination mode of the first state and the second state of each sensor, the sampling circuit generates one or more first detection signals.

[0019] Preferably, the first detection signal changes with the switching time of the first state and the second state of each of the sensors, or the first detection signal changes with the change of the combination mode of the first state and the second state of the sensor.

[0020] Preferably, the discharge rate of the body fluid includes a first discharge rate, and the calculation formula of the first discharge rate is:

[0021] Where n is the number of sensors, Tn represents the first detection signal, that is, the time when the nth sensor contacts the body fluid sample, Vn represents the volume of the body fluid sample when it reaches the nth sensor, K is a constant, and S 局部 Represents the area of the region for obtaining the body fluid sample.

[0022] Preferably, the body fluid sample further includes a second discharge rate, and the calculation formula of the second discharge rate is:

[0023] Where Is the contribution rate of the body fluid sample.

[0024] Preferably, the process of detecting the body fluid sample and generating the first detection signal further includes the following steps:

[0025] The body fluid sample sequentially passes through the detection points along a predetermined order;

[0026] Each detection point corresponds to a detection electrode of a sensor. When the body fluid sample reaches the detection electrode corresponding to the detection point, it contacts the sensor;

[0027] When the body fluid sample reaches the electrode corresponding to the detection point, the connection relationship between the sensor connected to the electrode and the reference circuit changes.

[0028] Preferably, the types of changes in the connection relationship between the sensor and the reference circuit include: changing from conducting to open or short - circuit, or from open to conducting or short - circuit, or from short - circuit to conducting or open.

[0029] Preferably, the body fluid detection method further includes the following steps:

[0030] The fluid collection component diverts the body fluid sample to the second detection circuit of the body fluid detection component;

[0031] After the second detection circuit comes into contact with the body fluid sample, the second detection signal is generated. The second detection signal is used to calculate the component content of the body fluid, and the second detection signal includes the sample components and the sample component content.

[0032] Preferably, the body fluid detection method further includes the following steps: The discharge rate of the body fluid and / or the content of at least some components of the body fluid are used to calculate the fatigue value, and the fatigue value includes the current fatigue value, single - time fatigue, and overall fatigue value.

[0033] Preferably, the calculation process of the current fatigue value includes:

[0034] Obtain the body fluid discharge rate, sample sodium ion concentration, and sample sweat sugar concentration as contribution indicators;

[0035] Obtain the contribution index weight rate, peak interval, and peak interval contribution weight rate;

[0036] Calculate the proportion of the peak interval time according to the current time and the peak interval at which this time is located;

[0037] Calculate the current fatigue value according to the proportion of the peak interval time and the peak interval contribution weight rate.

[0038] Preferably, the calculation process of the single - time fatigue value includes: Obtain the contribution index weight rate and at least one current fatigue value to calculate the single - time fatigue value.

[0039] The present invention also provides a body fluid detection device, which uses the body fluid detection method described in any of the embodiments for detection;

[0040] It includes the body fluid collection component and the body fluid detection component;

[0041] The body fluid collection component is used to obtain a body fluid sample;

[0042] The body fluid detection component is used to detect the body fluid sample and generate the first detection signal; the first detection signal is used to generate a biometric value; wherein, the biometric value includes at least one of the discharge rate, discharge volume, and fatigue value of the body fluid.

[0043] Advantages of the present invention:

[0044] Compared with the prior art, the body fluid detection method and detection device of the present invention can respectively detect a body fluid sample to obtain a first detection signal, and a physical sign value can be calculated through the first detection signal. The physical sign value can include the body fluid discharge rate, body fluid discharge amount, water balance, degree of hydration, fatigue value, etc., which is convenient for users and medical staff to monitor the degree of body fluid loss in the human body and supplement body fluid when the body fluid loss is excessive. In addition, the components of the body fluid can be detected through a second detection circuit, and the components of the body fluid can be used to calculate the content of the components, etc., so as to monitor the amount and content of the components in the body fluid by users and medical staff. When a certain component is missing, or the content is excessive or too little, operations such as controlling the component content are carried out in a timely manner. For example, when sodium ions or potassium ions are severely lost, sodium ions or potassium ions can be supplemented. BRIEF DESCRIPTION OF THE DRAWINGS

[0045] In order to more clearly illustrate the technical solutions of the present invention, the drawings of the invention will be briefly introduced below. Obviously, the drawings in the following description only relate to some embodiments of the present invention and do not limit the present invention.

[0046] Figure 1 Schematic diagram of a body fluid detection method in a preferred embodiment of the present invention;

[0047] Figure 2 Schematic diagram of the circuit of a body fluid detection device in a preferred embodiment of the present invention;

[0048] Figure 3 Schematic diagram of the internal circuit structure of a body fluid detection device in a preferred embodiment of the present invention. DETAILED DESCRIPTION OF THE EMBODIMENTS

[0049] The following will describe in detail the preferred embodiments of the present invention with reference to the accompanying drawings: It should be understood that the preferred embodiments are only for explaining the present invention and not for limiting the protection scope of the present invention.

[0050] Referring to Figure 1 , the present invention also provides a body fluid detection method including the following steps:

[0051] Step S1, obtaining a body fluid sample. For example, a body fluid sample can be obtained through a body fluid collection component, and the body fluid sample is in contact with a reference circuit. The collection component can be provided with a body fluid collection port, and a part of the reference circuit is located near the body fluid collection port or flush with the collection port. When the body fluid sample collected by the collection component enters the collection port, it can be in contact with the reference circuit. As Figure 1 shown, the reference resistor RE of the reference circuit is in contact with the body fluid sample, so that the detection device can record the time when the body fluid sample is in contact with the reference circuit.

[0052] Step S2, detect the body fluid sample and generate the first detection signal;

[0053] For example, the body fluid collection component can divert the body fluid sample to the first detection circuit 11 of the body fluid detection component. The body fluid collection component is provided with a diversion channel 210, and the body fluid sample reaches the first detection circuit 11 along the diversion channel 210. Through the diversion channel 210, the body fluid sample can reach the corresponding detection circuit in time, which is convenient for quickly detecting the body fluid sample and the overall characteristics of the human body fluid. The overall characteristics of the human body fluid can include the physical sign values, body fluid components, body fluid component contents, etc. as described above.

[0054] Step S3, the first detection signal is used to generate a biological sign value; wherein, the biological sign value includes at least one of the excretion rate, excretion amount, and fatigue value of the body fluid. For example, after the first detection circuit 11 contacts the body fluid sample and generates the first detection signal, the first detection signal is used to calculate the excretion rate of the body fluid. It can contact the first detection circuit 11, so that it can record at least one of the information such as the contact time between the body fluid and the first detection circuit 11, the voltage value, resistance value, or current value change of the first detection circuit 11 as the first detection signal.

[0055] As a preferred embodiment, the first detection circuit 11 includes at least one sensor and a sampling circuit; the process of generating the first detection signal includes the following steps:

[0056] When the first detection circuit 11 contacts the body fluid sample, the first state and the second state of at least one of the sensors are switched; at least one of the sensors is used to detect the body fluid sample, and the first state and the second state of at least one of the sensors are switched; the body fluid sample sequentially passes through the detection points in a predetermined order and is electrically connected to the corresponding sensors at each detection point; the sensors in contact with the body fluid sample are switched between the first state and the second state; according to the switching times of the first state and the second state of each of the sensors, the sampling circuit generates one or more first detection signals, or according to the combination mode of the first state and the second state of each sensor, the sampling circuit generates one or more first detection signals. Wherein, the sensors can be arranged in sequence along the flowing direction of the body fluid sample, or the first connecting part or the second connecting part of the sensor extends into the diversion channel 210 to form a detection electrode. The number of the detection electrodes is multiple, and the body fluid sample can contact the detection electrodes in sequence. When the corresponding detection electrode contacts the body fluid sample, the connection state between the sensor and the reference resistor changes. For example, when the body fluid sample contacts, such as Figure 1When contacting the detection electrode shown at detection point A1, the connection state between the first sensor R1 and the reference resistor RE will change as follows: from conducting to disconnected or short-circuited, or from disconnected to conducting or short-circuited, or from short-circuited to conducting or disconnected. When the connection state between the sensor R1 and the reference resistor RE changes, the first state and the second state of the sensor will switch.

[0057] According to the switching time of the first state and the second state of each sensor, the sampling circuit generates one or more first detection signals, or according to the combination mode of the first state and the second state of each sensor, the sampling circuit generates one or more first detection signals. For example, when the first sensor R1 contacts the body fluid sample (i.e., when the body fluid sample reaches the detection point A1), the first sensor R1 can switch from the first state to the second state. At this time, at least one of the voltage value, resistance value, and current value of the first detection circuit 11 will change. At this time, the detection device can record the switching time, the voltage value before or after switching, the resistance value before or after switching, the current value before or after switching, the voltage change value after switching, the resistance change value after switching, the current change value after switching, etc., as the first detection signal. For example, when calculating the body fluid discharge rate, the switching time can be taken as the first detection signal.

[0058] In order to improve the detection accuracy, the detection method of the present invention collects body fluid samples through multiple sensors to form multiple first detection signals, and then calculates the discharge rate of body fluid in a certain period according to the multiple first detection signals. The first detection signal changes with the switching time of the first state and the second state of each sensor, or the first detection signal changes with the change of the combination mode of the first state and the second state of the sensor. The first detection signal can calculate the physical sign value, and the physical sign value can include the body fluid discharge rate, the body fluid discharge amount, the water balance, the degree of hydration, etc.

[0059] The discharge rate of the body fluid includes the first discharge rate. The method for calculating the first discharge rate is as follows: record the time T1, T2,..., T when the sweat flows to A1, A2,..., A n Since the internal space of the diversion channel 210 is fixed, when the body fluid flows into the diversion channel 210, the volume V of the body fluid sample can be calculated according to the position where it arrives. n For example, when the cross-section of the diversion channel 210 is circular, the volume V of the body fluid sample can be calculated according to the radius r or diameter d of the diversion channel 210 and the position where the body fluid sample reaches the nth sensor, and the position of the detection device (such as the arm, head, back, etc.) can be calculated. n n n Alternatively, when the cross-section of the diversion channel is rectangular, the volume V of the body fluid sample can be calculated based on the width a and height b of the diversion channel, as well as the distance S that the body fluid sample flows through in the diversion channel n -S n-1 at the location of the detection device (such as the arm, head, back, etc.). n , v n =(S n -S n-1 )×a×b. Of course, the cross-sectional shape of the diversion channel can be other geometric shapes. Since the cross-sectional area is fixed before the production of the detection device, the cross-sectional area S can be set in advance, so that for the volume V of the body fluid sample n only the distance S that the body fluid sample flows through in the diversion channel needs to be known n -S n-1 to calculate v n =(S n -S n-1 )×S. Then, based on the volume V n per unit time T n -T n-1 of the sweating rate v per unit area can be calculated n_water_local . The formula for calculating the first discharge rate is:

[0060] where n is the number of sensors, Tn represents the first detection signal, i.e., the time when the nth sensor contacts the body fluid sample, Vn represents the volume of the body fluid sample when it reaches the nth sensor, K is a constant, and S 局部 represents the area of the sweat collection area of the body fluid detection device (for example, this area can be the area of the body fluid detection device covering the human skin, or the area of the collection component or the sensor substrate covering the human skin, etc.), unit: m 2 . For example, K can take values from 100 to 2000 and can be adjusted to other constants according to the actual situation, such as 1000, etc. It should be noted that the formula for calculating the first discharge rate can be Formula 1 as described above.

[0061] The discharge rate also includes a second discharge rate, and the formula for calculating the second discharge rate is:

[0062] where is the contribution rate of the body fluid sample. Using the contribution rate the whole-body sweating rate v is inversely calculated from the local sweating rate n_water_whole , unit: mL / m 2 / h. The It can be a positive number, for example, it can take values such as 0.1 - 10 or 10 - 50, etc. Of course, it can also be set or modified according to actual needs. The second excretion rate can be the overall body fluid excretion rate of the human body during a certain period. For example, the overall excretion rate of human sweat during the period of running a 5 - kilometer distance. It should be noted that the calculation formula of the second excretion rate can also be Formula 2 described below.

[0063] Excretion amount of total body fluid (such as water loss due to sweating all over the body): The total sweating amount V can be deduced through the total body fluid excretion rate and the body surface area of the human body n waterloss , unit: mL, where the body surface area of the human body can be calculated from height and weight, with reference to Formulas 3 and 4 combined;

[0064]

[0065] S BSA =a×H×bM - c (Formula 4)

[0066] Among them, T n represents the total duration of response at the nth sweat measurement point A n or the time as described above, unit: h;

[0067] n' can be a positive integer, for example, its value can be 1 - 50. a / b / c can be numbers greater than 0 respectively, and their value ranges can be [0,1] respectively. For example, a = 0.00061, b = 0.0128, c = 101529.

[0068] S BSA represents the body surface area of the measured human body, unit: m 2 ;

[0069] H represents the height of the measured human body, unit: cm;

[0070] M represents the weight of the measured human body, unit: kg.

[0071] Total body water balance: The difference between the total loss and total intake of water, where the total loss includes sweat loss and sweat runoff, unit: ml, with reference to Formulas 5 - 7 combined

[0072] BAL water =TotalV waterloss -TotalV waterintake (Formula 5)

[0073] TotalV waterloss =V nwaterloss +V urine (Formula 6)

[0074]

[0075] Where: n represents the number of times of liquid intake, including before exercise, during exercise, and after exercise;

[0076] V nfluid_intake represents the volume of the nth liquid intake, unit: mL

[0077] V urine represents the urine output, unit: ml, and the urine output can be entered according to the actual situation.

[0078] Calculation of hydration level: The percentage of the total mass of water loss in the total body weight, referring to Formula 8

[0079]

[0080] Where: M - body weight, unit: kg.

[0081] To improve the practicality of the detection device, the detection method further includes the following steps:

[0082] The liquid collection component guides the body fluid sample to the second detection circuit of the body fluid detection component;

[0083] After the second detection circuit comes into contact with the body fluid sample, the second detection signal is generated, and the second detection signal is used to calculate the component content of the body fluid. The second detection signal can be the components of the body fluid sample and the component content of the body fluid sample. Through the components of the body fluid sample and the component content of the body fluid sample, the components of the human body fluid and the component content of the body fluid are calculated. The following explains the method and process of calculating the components of the human body fluid and the component content of the body fluid through the calculation processes such as the sodium ion concentration of the whole body fluid, the potassium ion concentration of the whole body fluid, the glucose concentration of the whole body fluid, the total sodium ion loss of the whole body, the total potassium ion loss of the whole body, the total glucose loss of the whole body, sodium balance, potassium balance, or glucose balance, etc., and can refer to the following:

[0084] Sodium ion concentration of the whole body fluid: The second detection circuit of the detection device can use a sensor prepared by the principle of ion-selective electrode to detect the sodium ion concentration C of the local sweat sample in real time Na_local , unit mmol, referring to the public

[0085] Formula 9

[0086]

[0087] Potassium ion concentration of the whole body fluid: The second detection circuit of the detection device can use a sensor prepared by the principle of ion-selective electrode to detect the potassium ion concentration C in the sweat sample of the local detection area in real time K_local , unit mmol, and then use the contribution rate to inversely calculate the potassium ion concentration C of the whole body sweatingK_whole , in mmol, referring to Formula 10

[0088]

[0089] Total body fluid glucose concentration: The device uses a sensor prepared based on the principle that glucose oxidase catalyzes the oxidation reaction of glucose to generate a microcurrent to detect the sweat glucose concentration C in the local detection area in real time GLU_local , in μmol, and then uses the contribution rate to inversely calculate the total body sweating glucose ion concentration C GLU_whole , in μmol, referring to Formula 11

[0090]

[0091] Total body sodium loss: Calculate the total body sodium sweating loss M from the total body sweat sodium concentration and the total body sweating volume Na+loss , unit: mg, can refer to Formula 28 or Formula 12;

[0092]

[0093] where A1 is a positive integer, and its value range can be [10, 100]. For example, the said A1 can be 23. The value range of K1 can be [100, 2000]. For example, the said K1 can be 1000.

[0094] Total body potassium loss: Calculate the total body potassium sweating loss M from the total body sweat potassium concentration and the total body sweating volume K+loss , unit: mg, can refer to Formula 13 or Formula 29;

[0095]

[0096] where A2 is a positive integer, and its value range can be [10, 100]. For example, the said A2 can be 39. The value range of K2 can be [100, 2000]. For example, the said K2 can be 1000.

[0097] Total body glucose loss: Calculate the total body glucose sweating loss M from the total body sweat glucose concentration and the total body sweating volume GLU_loss , unit: mg, referring to Formula 30 or Formula 14;

[0098]

[0099] where A3 is a positive integer, and its value range can be [10, 300]. For example, the said A2 can be 180. The value range of M can be [10, 200]. For example, the said M can be 100.

[0100] Total body sodium balance: The difference between the total sodium loss and the total sodium intake, where the total loss includes sweat loss and sweat drainage. Since the detection method of sodium ion concentration in sweat is limited, this algorithm ignores it. Unit: mg. Refer to Formula 15 - 17 or Formula 31 - 33;

[0101] BAL n Na = TotalM Naloss - TotalM Naintake (Formula 15)

[0102] Total M Naloss = M nNaloss (Formula 16)

[0103]

[0104] Where: n represents the number of times of fluid intake, including before exercise, during exercise, and after exercise. Unit: ml;

[0105] P nNa1 represents the percentage of ionic sweat in the fluid, relying on the value saved by the user input or the system record of the previous exercise. Unit: mg;

[0106] The value range of K3 can be [100, 2000]. For example, the said M can be 1000.

[0107] Total body potassium balance: The difference between the total potassium loss and the total potassium intake, where the total loss includes sweat loss and sweat drainage. Since the detection method of potassium ion concentration in sweat is limited, this algorithm ignores it. Unit: mg. Combined with reference to Formula 34 - 36 or reference to Formula 18 - 20;

[0108] BAL n K = TotalM Kloss - TotalM K-intake (Formula 18)

[0109] Total M Kloss = M nKloss (Formula 19)

[0110]

[0111] Where: n represents the number of times of sweat intake, including before exercise, during exercise, and after exercise. Unit: ml;

[0112] P nK represents the percentage of ionic sweat in the fluid, relying on the value saved by the user input or the system record of the previous exercise. Unit: mg;

[0113] As a preferred embodiment, the body fluid detection method further includes the following steps: the discharge rate of the body fluid and / or the content of at least some components of the body fluid are used to calculate the fatigue value.

[0114] The liquid collection component diverts the body fluid sample to the second detection circuit;

[0115] After the second detection circuit comes into contact with the body fluid sample, the second detection signal is generated. The second detection signal is used to calculate the component content of the body fluid, and the second detection signal includes the sample components and the sample component content.

[0116] The discharge rate of the body fluid and / or the content of at least some components of the body fluid are used to calculate the fatigue value, and the fatigue value includes the current fatigue value, single fatigue, and overall fatigue value.

[0117] The calculation process of the current fatigue value includes:

[0118] Obtain the body fluid discharge rate, sample sodium ion concentration, and sample sweat sugar concentration as contribution indicators;

[0119] Obtain the contribution index weight rate, peak interval, and peak interval contribution weight rate;

[0120] Calculate the proportion of the peak interval time according to the current time and the peak interval at which the time is located;

[0121] Calculate the current fatigue value according to the proportion of the peak interval time and the peak interval contribution weight rate.

[0122] The calculation of the fatigue value: The algorithm framework: TRIMP peak interval time ratio weighting can be adopted. The weighting value can adopt the score interval: 0 to M'. The M' can be a positive integer. For example, the value range is [1, 50]. Preferably, M' takes the value of 21. The score period is divided into several levels. For example, it is divided into four levels as shown below. The fatigue level of the user can be obtained according to the fatigue value calculated as follows, so as to estimate the degree of exercise that oneself can do. The fatigue levels can include: Light (0 - 9.9); Moderate (10 - 13.9); Strenuous (14 - 17.9); AllOut (18 - 21). The user can control their exercise amount with reference to the fatigue level. If the fatigue value is 16, then the user's level is Strenuous (14 - 17.9). Different fatigue values correspond to different exercise intensities. For example, the exercise intensity of Light (0 - 9.9) can be less than that of Moderate (10 - 13.9).

[0123] The fatigue value can be calculated through the contribution index of the fatigue value, the contribution index weight rate, the peak interval, the peak interval contribution weight rate, the time proportion of the peak interval, etc. The fatigue value includes at least one of the fatigue value of a single index, the overall fatigue value of a single exercise, or the overall fatigue value of multiple exercises in a day. The fatigue value of a single index can refer to the fatigue value at a certain time point T n of the fatigue value.

[0124] Among them, the contribution index of the fatigue value, the contribution index weight rate, the peak interval, and the peak interval contribution weight rate can be the contribution index, contribution index weight rate, peak interval, and peak interval contribution weight rate described above, which will not be elaborated here; the time proportion of the peak interval PoT can be calculated through the time and the peak period of this time, and can refer to Formula 21

[0125]

[0126] Specifically, the fatigue value Fatigue of a single index indexm (the current fatigue value at a certain time) can be calculated through the time proportion of the peak interval and the peak interval contribution weight rate, and can refer to Formula 37 or the public

[0127] Formula 22:

[0128]

[0129] Among them, the "n" can be a positive integer, for example, the value range is [1, 10]. Preferably, the value of "n" is 5; the A4 can be a positive integer, for example, the value range is [10, 80]. Preferably, the value of A4 is 21.

[0130] The calculation process of the single fatigue value includes: obtaining the contribution index weight rate and at least one current fatigue value to calculate the single fatigue value. Specifically, the overall fatigue value (single fatigue value) Fatigue of a single exercise can be calculated through the fatigue value of a single index and the contribution index weight rate, and can refer to Formula 38 or 23:

[0131]

[0132] The "n''" can be a positive integer, for example, the value range is [1, 10]. Preferably, the value of "n''" is 3.

[0133] The algorithm for the overall fatigue value of multiple exercises in a day: Integrate the time of multiple exercises and regard it as a single exercise for interval weighting. The calculation process can refer to Formula 23 or Formula 38.

[0134] Regarding the acquisition of exercise duration, it includes one or more combinations of the following solutions: ① Operating on the APP side or the application terminal device to calculate the exercise duration through manual start and end operations; ② Adding a G-sensor to the host device to determine whether the user switches the exercise state.

[0135] The detection method of the present invention calculates multiple detection results such as biometric values, liquid components, and component contents through the first detection signal of the first detection circuit and the second detection signal of the second detection circuit. The biometric values include at least one of local sweating rate, whole body sweating rate, whole body sweating amount (whole body sweating water loss amount), whole body water balance, degree of hydration, and fatigue value, etc. The content of the sweat components may include at least one of sodium ion concentration, potassium ion concentration in sweat, glucose concentration, sodium ion sweating loss amount, potassium ion sweating loss amount, glucose sweating loss amount, sodium balance, potassium balance, etc. The detection method provided by the present invention can non-invasively obtain a body fluid sample, and then analyze the body fluid sample to obtain indicators such as the biometric value, the components of the liquid, and the component content, so that the person being tested or medical staff can judge the current physical condition of the human body, whether the human body needs to supplement water, whether it needs to supplement energy, etc. In particular, by calculating the fatigue value, it is possible to judge the single-time exercise duration of a person and whether rest is needed, etc.

[0136] Refer to Figure 2 And Figure 3 In this embodiment, a body fluid detection device is provided, which includes a body fluid detection component 1 and a body fluid collection component 2. The body fluid detection component 1 is connected to the body fluid collection component 2. For example, all or part of the components of the body fluid detection component 1 are installed on the body fluid collection component 2. The body fluid collection component 2 is used to obtain a body fluid sample. The body fluid detection component 1 obtains the body fluid sample collected by the body fluid collection component 2. The body fluid detection component 1 can be used to detect and analyze the body fluid sample collected by the body fluid collection component 2 to generate a corresponding detection signal, and a corresponding detection result can be generated according to the detection signal. Corresponding prompts can be made according to the detection result. For example, the first detection signal can be generated according to the time or speed at which the body fluid sample flows through some components of the body fluid detection component (such as the sensors described below), and the excretion rate of the body fluid can be calculated through the first detection signal. The excretion amount of the body fluid in a certain period can be calculated according to the excretion rate or the first detection signal. The excretion rate can be at least one of the local body fluid excretion rate or the whole body body fluid rate of the person being tested. The excretion amount can be at least one of the local body fluid excretion amount or the whole body body fluid amount of the person being tested.

[0137] The body fluid detection component 1 includes a reference circuit 13 and a first detection circuit 11, and the reference circuit 13 is connected to the first detection circuit 11. The first detection signal is generated according to the reference circuit 13 and the first detection circuit 11, and the first detection signal is used to generate a biometric value. It should be noted that the biometric value can be directly or indirectly generated using this first detection signal, and some biometric values require the cooperation of the first detection signal and other signals to generate. For example, the first detection signal can be used to calculate the local excretion rate (the first excretion rate) of the body fluid, and the overall excretion rate (the second excretion rate) can be calculated through this local excretion rate. The body fluid sample can be in contact with the reference circuit 13 and the first detection circuit 11. After the body fluid sample is in contact with the reference voltage and the first detection circuit 11, the first detection signal can be generated. By the cooperation of the reference circuit 13 and the first detection circuit 11 to generate the first detection signal, the accuracy and efficiency of the detection device can be effectively improved, and the interference from the outside to the first detection signal can also be effectively reduced. The first detection signal can be one or more of a time signal, a digital signal, an electrical signal, etc. As a preferred embodiment, part of the reference circuit 13 and the first detection circuit 11 can be installed in the body fluid collection component, so as to quickly detect the body fluid sample and improve the detection efficiency and accuracy.

[0138] As a preferred embodiment, the first detection circuit 11 includes at least one sensor and a sampling circuit 14, and at least one of the sensors is connected to the sampling circuit 14. Preferably, each of the at least one sensors can be installed in the body fluid collection component. Each of the sensors can be a resistor (R1-Rn). The sampling circuit 14 can include a sampling resistor R0 and a sampling point. The sampling resistor R0 is grounded, and the sampling resistor R0 is connected to at least one of the sensors. The sampling point is located between the sampling resistor R0 and at least one of the sensors; the first detection signal can be formed or obtained according to the voltage or current change at the sampling point. By forming or obtaining the first detection signal through the sampling circuit 14, the processing time and space of the body fluid detection device for the signal can be reduced, thereby improving the accuracy of the body fluid detection device.

[0139] As a preferred embodiment, each of the sensors is used to generate a first state and a second state according to the state of detecting the body fluid sample. For example, before the sensor is in contact with the body fluid sample (or the sensor is not in contact with the body fluid sample), the sensor is in the first state, and when the sensor is in contact with the body fluid sample, the sensor is in the second state. Or, before the sensor is in contact with the body fluid sample, the sensor is in the second state, and when the sensor is in contact with the body fluid sample, the sensor is in the first state. Since each sensor can switch states, the first detection signal can be generated according to the state switching of each sensor.

[0140] For example, a first detection signal can be formed by combining the first state and the second state of the sensor. The combination method can be 2 n kinds. When the first detection signal is an electrical signal, different combination methods can respectively form a first detection signal. The body fluid discharge rate can be calculated based on the generation time of the first detection signal or the time difference between adjacent combination states. For example, when the number of sensors is three, the combination methods can include 8, as shown in Table 1 below (0 represents the first state, 1 represents the second state):

[0141] Sensor Serial Number / Combination Method R1 R2 R3 Combination 1 0 0 0 Combination 2 0 0 1 Combination 3 0 1 1 Combination 4 0 1 0 Combination 5 1 0 0 Combination 6 1 0 1 Combination 7 1 1 0 Combination 8 1 1 1

[0142] Table 1

[0143] In addition, one or more first detection signals can be generated by the sampling circuit 14 according to the different switching times of the first state and the second state of each sensor. For example, the sensors (R1 / R2 / R3) switch states (from the first state to the second state or from the second state to the first state, etc.) at three time points or time periods T1 / T2 / T3 respectively, so that the first detection signal can be T1 / T2 / T3 or T1 / T2 - T1 / T3 - T2, etc.

[0144] As a preferred embodiment, the number of the sensors is two or more; each sensor is arranged in a predetermined order. As Figure 1 shown, the sensors (R1-Rn) are arranged in parallel in sequence along the flowing direction of the body fluid sample. When the first detection circuit 11 receives the body fluid sample, the body fluid sample contacts each sensor in sequence. Taking three sensors (R1 / R2 / R3) as an example, when a first detection signal can be respectively formed according to different combination methods, the first detection signal can be one or several of combinations 5, 7, and 8 in Table 1, or generated according to one or several of combinations 5, 7, and 8. When the switching times of the first state and the second state of the first detection signal sensor are different, the first detection signal T1 / T2 / T3 or T1 / T2 - T1 / T3 - T2, etc. can also be the time when the body fluid sample contacts the sensors (R1 / R2 / R3) respectively, or the time difference between adjacent two sensors (except the first sensor, taking the time when the first sensor contacts the body fluid sample).

[0145] Preferably, the first detection signal is a variable signal. As described above, since the contact time between the body fluid sample and each sensor of the first detection circuit 11 is different, the switching time of each sensor between the first state and the second state is also different. Therefore, the first detection signal can vary with the switching time of each sensor between the first state and the second state, or the first detection signal varies with the change in the combination mode of the first state and the second state of the sensor.

[0146] Since the number of the sensors can be multiple, at least one of the sensors includes a first sensor, a second sensor, …, an nth sensor. Each sensor (R1 / R2 / R3…Rn) respectively includes a first connection end and a second connection end. For example, referring to Figure 1 , the first sensor R1 includes a first connection end 01 and a second connection end 02. In the first state and the second state of the first sensor: the first connection end 01 of the first sensor R1 is connected to the reference circuit 13; the second connection end 02 of the first sensor R1 is connected to the first connection end of the second sensor R2, and a detection point A1 is formed. The second connection end of the second sensor R2 is connected to the first connection end of the third sensor R3, and a detection point A2 is formed... And so on, the second connection end of the (n - 1)th sensor Rn - 1 is connected to the first connection end of the nth sensor Rn, and a detection point An - 1 is formed; the detection circuit of the nth sensor Rn is connected, and a detection point A0 is formed. When all the sensors are in the first state, the sensors are in series in sequence. In the first state, there is a gap between the second connection end of each sensor and the detection circuit. Preferably, in the first state, the second connection end of each sensor is disconnected from the detection resistor RE. When a certain sensor is in the second state, the sensor can be short-circuited through the body fluid sample in a manner similar to the short circuit of the first sensor. For example: the second connection end of the first sensor R1 can connect the second terminal 02 of the first sensor R1 to the reference circuit 13 or its first terminal 01 through the body fluid sample in the second state, so that the first sensor R1 is short-circuited. As a preferred embodiment, the nth sensor can be connected to the sampling resistor R0 of the sampling circuit 14.

[0147] The body fluid detection component further includes a second detection circuit 12, and the second detection circuit 12 shares the reference circuit 13 with the first detection circuit 11. After contacting the body fluid sample, the second detection circuit 12 generates a second detection signal, and the second detection signal is used to calculate the component content of the body fluid. The second detection signal can also be used to detect the components of the body fluid sample. The second detection circuit 12 can analyze the components in the body fluid sample by using the electrochemical method: one, two, or any combination of two or more of glucose, lactic acid, uric acid, pH, potassium ion, sodium ion, calcium ion, chloride ion, cortisol, neuropeptide Y, heavy metal ions As, Hg, or Pb, and analyze the concentration of each component. As Figure 1 , the detection terminal WE1 of the second detection circuit can be used to detect glucose, the detection terminal WE2 can be used to detect lactic acid, the detection terminal WE3 can be used to detect potassium ions, the detection terminal WE4 can be used to detect sodium ions, the detection terminal WE5 can be used to detect pH, and so on. Currently, the technologies for calculating the components and component content of the body fluid sample will not be elaborated here. Hereinafter, we use the components and component content in the body fluid sample as the second detection signal to analyze the content and content components of the body fluid.

[0148] By sharing a reference circuit 13 between the first detection circuit 11 and the second detection circuit 12, both the first detection circuit 11 and the second detection circuit 12 use the voltage of the reference circuit 13 as the reference voltage, so that there is only one reference point where the body fluid sample can reach, thereby avoiding the instability of the body fluid detection device caused by the mutual influence between multiple potentials, and further improving the stability and reliability of the body fluid detection device. The positional relationship between the first detection circuit 11 and the second detection circuit 12 can be set as needed. The preferred implementation in this embodiment is that along the flowing direction of the body fluid sample, the second detection circuit 12 is located in front of the first detection circuit 11, that is to say, the second detection circuit 12 can contact the body fluid sample earlier than the first detection circuit 11. In this way, the bubbles in the body fluid sample contacted by the first detection circuit 11 can be reduced, ensuring that the first detection circuit 11 can fully contact the body fluid sample, thereby improving the stability and reliability of the first detection circuit 11.

[0149] The reference circuit 13 may include a reference resistor RE, and the reference resistor RE is installed on the acquisition component. The reference resistor RE is connected to the first terminal of the first sensor.

[0150] As a preferred embodiment, the acquisition component includes a sensor substrate 21. Each of the sensors is respectively printed on the sensor substrate 21, and the load of the sampling circuit 14 is printed on the sensor substrate 21 or mounted on a carrier outside the sensor substrate 21. The sensor substrate 21 can be made of a flexible material, so that the sensor substrate 21 has better adaptability and improves the acquisition of body fluids by the acquisition component. The reference resistor RE, the first sensor, the second sensor... the nth sensor are respectively arranged on the sensor substrate 21. Preferably, the first sensor, the second sensor... the nth sensor and the sampling resistor R0 are all printed on the sensor substrate 21. Considering that when printing components such as the first sensor, the second sensor... the nth sensor and the sampling resistor R0, the resistance values of the components of the sensor substrate 21 produced in different batches may deviate during the production process. However, the resistance values of the first sensor, the second sensor... the nth sensor and the sampling resistor R0 in the same batch are usually larger or smaller as a whole. Therefore, it is preferred to print the sampling resistor R0 together with the sensors on the sensor substrate 21. The advantage of this treatment is that since the resistance values of the first sensor, the second sensor... the nth sensor and the sampling resistor R0 in the same batch are usually larger or smaller as a whole, when mass-producing the detection device, the voltage of the reference circuit 13 is relatively stable. Of course, the sampling resistor R0 can also be placed on other components of the detection device, such as on a PCB board other than the sensor substrate 21.

[0151] As a preferred embodiment, a flow channel 210 can be provided on the sensor substrate 21, and the body fluid sample can flow in the flow channel 210. The first connection ends and the second connection ends of the reference resistor RE, the first sensor, the second sensor... the nth sensor are respectively located in the flow channel 210. When there is a body fluid sample in the flow channel 210, the body fluid sample can contact all or part of the first connection end or the second connection end of the reference resistor RE and each sensor.

[0152] The detection device can include a main unit, and the main unit can be connected to at least one of the first detection circuit 11, the second detection circuit 12 and the reference circuit 13. The discharge rate of the body fluid and / or the content of at least part of the components of the body fluid are used to calculate the fatigue value. The discharge rate, discharge amount, components and component content of the body fluid can be completed in the main unit of the detection device or can be completed by an external device. The internal functional modules of the main unit include an electrochemical processing module, an acceleration sensor G-sensor, etc.

[0153] Each sensor (R1, R2, ……, Rn, n is a natural number) provided on the sensor substrate 21 may be a high-value resistor, and the resistance value of each high-value resistor R1, R2, ……, Rn is between 100 K ohms and 50 M ohms. Both poles of each high-value resistor are paired electrodes by the circuit of the electrode layer, and each electrode is respectively led out into the diversion channel to form body fluid detection electrode pairs A1, A2, ……, An-1. In order to prevent interference between electrodes, gaps can be formed between each electrode pair. In order to improve the speed of detecting body fluid samples and minimize the volume of the detection device as much as possible, the distance between the two terminals of the detection electrode pair is 0.05 mm to 1 mm. When a body fluid sample reaches the area with electrode pairs, the body fluid sample can cover the detection electrode pair to form a short circuit, that is, an open circuit becomes a short circuit. The body fluid sample flows through different areas of the diversion channel in sequence, and the sampling circuit 14 detects changes in the resistance value, voltage value or current value of the series-connected high-value resistors, and the physical sign value can be calculated according to at least one of the change time, resistance value, voltage value or current value. For example, the sampling circuit 14 can send at least one of the change time, resistance value, voltage value or current value to the main control circuit of the host, thereby realizing the calculation of the physical sign value. It is also possible to obtain the change in the resistance value, voltage value or current value or the change time (the first detection signal) detected by the sampling circuit 14 through the terminal device, thereby realizing the calculation of the sweating amount. The resistance values of the high-value resistors R1, R2, ……, Rn are preferably 3 M ohms to 10 M ohms; of course, according to needs, the high-value resistors R1, R2, ……, Rn can also be set to different measurement levels.

[0154] Preferably, referring to Figure 2, the diversion channel is serpentinely arranged. Using high-resistance conductive ink, one or more serially connected high-value resistors R1, R2, ……, Rn are prepared, where n is a natural number, and the resistance value of each high-value resistor R1, R2, ……, Rn is between 10K ohms and 10M ohms. The two poles of each high-value resistor are led out in pairs by the circuit of the electrode layer to the diversion channel to form detection electrode pairs. The distance between the two terminals of the detection electrode pair is between 0.3 mm and 10 mm. A water-soluble conductive paste is made between the detection electrode pairs, and a short circuit is formed between the detection electrode pairs, so that all the high-value resistors are in an invalid bypass state; when a body fluid sample reaches the area where each detection electrode pair is located, the body fluid sample will dissolve and carry away the conductive paste between the detection electrode pairs, that is, the short circuit becomes an open circuit, which means that each sensor is converted from the second state to the first state. The body fluid samples reach each detection electrode pair and different-level sweat volume detection areas continuously in sequence, opening the high-value resistors in sequence. The sampling circuit 14 can timely detect at least one increase in the resistance value, voltage, or current of the series resistors, and can calculate the physical sign value according to at least one of the changing time, resistance value, voltage value, or current value. The sampling circuit 14 can also send at least one of the changing time, resistance value, voltage value, or current value to the main control circuit of the host, or the host sends the changing time, resistance value, voltage value, or current value to the main control circuit of the terminal, thus realizing the calculation of the physical sign value.

[0155] The resistance values of the high-value resistors R1, R2, ……, Rn are preferably 100K ohms to 1M ohms.

[0156] The main control circuit of the host can timely detect an increase in the resistance value of the series resistors. The increased resistance is the parallel resistance of the corresponding high-value resistor and the solution resistance between the terminal pairs.

[0157] Definition of different-level sweat volume detection areas: Sweat enters the sweat channel from the sweat inlet. The system can detect the time when the sweat detection point and the sweat volume detection points R1~Rn are reached, and can calculate the time when the sweat fills the entire channel or a part of the channel, and then can calculate the flow rate of the sweat in the channel, and can estimate the sweating rate p; in combination with the user's exercise duration, the sweat volume can be roughly estimated. The exercise duration t is obtained from the acceleration sensor G-Sensor inside the host and / or the data input by the user (such as exercise mode selection, start and end actions). The proportion β of the sweat volume in the sweat collection area to the sweat volume of the whole body is obtained by fitting experimental data and empirical formulas, so as to realize the detection of different-level sweat volumes V.

[0158] V = p × t / β

[0159] Furthermore, by combining information such as the user's exercise type, BMI index, exercise intensity, external environment, and data statistics at different time periods, deeper data analysis can be performed, such as the matching degree between exercise items and exercise intensity, the time-space distribution of group data, and group physical fitness screening.

[0160] Taking the detection of human sweat as an example, the working principle of the detection device of the present invention will be further described below.

[0161] According to the actual situation, the detection device is set at any one or more positions of the human hand, back, chest, abdomen, or leg, etc., to detect the corresponding positions. When sweat is discharged, the sweat can be collected by the collection component, and the collected body fluid sample enters the diversion channel 210 on the sensor substrate 21, and the body fluid sample can flow in the diversion channel 210. The body fluid sample is in turn connected to the reference resistor RE, the first sensor, the second sensor... the first connection end and the second connection end of the nth sensor.

[0162] When the sweat flows through the diversion channel 210 and contacts or conducts with the first sensor, the second sensor... the nth sensor in turn, for example, when the sweat passes through Figure 1 the positions A1, A2, A3,..., An, A0 shown, the voltage sampling values collected by the sampling points ADC of the sampling circuit 14 change in turn; specifically, the voltage sampling values change in turn as follows:

[0163] ① When the sweat does not enter the channel, the ADC sampling value V = V_re*R0 / (R1 + R2 +... + Rn + R0)

[0164] ② When the sweat enters the position A1, the ADC sampling value V = V_re*R0 / (R2 +... + Rn + R0)

[0165] ③ When the sweat enters the position A2, the ADC sampling value V = V_re*R0 / (R3 +... + Rn + R0)

[0166] ……

[0167] ④ When the sweat enters the position An, the ADC sampling value V = V_re*R0 / (Rn + R0)

[0168] ⑤ When the sweat enters the position A0, the ADC sampling value V = V_re

[0169] Wherein: V_re represents the voltage value of the reference circuit 13, R1, R2,..., Rn respectively represent the resistance values of n sensors, and R0 represents the resistance value of the load of the sampling circuit 14.

[0170] Furthermore, if it is necessary to improve the resolution of a certain detection site, it can be achieved by adjusting the corresponding resistance.

[0171] For example: Assume that V_re = 1.5V; there are a total of 10 detection sites, and R1 = R2 = … = R10 = R; R0 = 4R, and the voltage at the sampling point is V;

[0172] ① When no sweat enters the channel, V = V_re * R0 / (R1 + R2 + … + R10 + R0) = 1.5V * 4R / 14R = 0.429V

[0173] ② When sweat enters position A1, V = V_re * R0 / (R2 + … + R10 + R0) = 1.5V * 4R / 13R = 0.462V

[0174] ③ When sweat enters position A2, V = V_re * R0 / (R3 + … + R10 + R0) = 1.5V * 4R / 12R = 0.5V

[0175] ……

[0176] ④ When sweat enters position A10, V = V_re * R0 / (R10 + R0) = 1.5V * 4R / 5R = 1.2V

[0177] ⑤ When sweat enters position A0, V = V_re = 1.5V

[0178] As can be seen from the above, when sweat enters A1, the change in voltage is 0.462 - 0.429 = 0.033V; if the sensitivity of point A1 is to be provided, the resistance R1 can be increased. Assume that R1 = 5R; then

[0179] ① When no sweat enters the channel, V = V_re * R0 / (R1 + R2 +.. + R10 + R0) = 1.5V * 4R / 18R = 0.333V

[0180] ② When sweat enters position A1, V = V_re * R0 / (R2 +.. + R10 + R0) = 1.5V * 4R / 13R = 0.462V

[0181] Then the change in voltage when sweat flows through point A1 is 0.462 - 0.333 = 0.129V, and the sensitivity of this site is greatly improved.

[0182] The first detection signal shown may include the voltage V collected by the sampling circuit 14 at different time points as described above, may also include the circuits collected by the sampling circuit 14 at different time points, and may also include the times T1, T2, T3, …, Tn, T0 when sweat reaches A1, A2, A3, …, An, A0 in the diversion channel 210.

[0183] Such as Figure 1In the present embodiment, along the direction of the flow of the body fluid sample, the second detection circuit 12 is located in front of the first detection circuit 11. That is to say, the second detection circuit 12 first detects the sweat, so as to obtain detection results such as the components of the body fluid sample. For example, the components of the body fluid sample may include one, two, or any combination of two or more of water, glucose, lactic acid, uric acid, pH, potassium ions, sodium ions, calcium ions, chloride ions, cortisol, neuropeptide Y, heavy metal ions such as As, Hg, or Pb. Therefore, the sweat can first be detected by the second detection circuit 12 and then enter the first detection circuit 11 for detection.

[0184] Since the first detection circuit 11 does not separately introduce a reference circuit, but electrically shares the reference circuit with the second detection circuit 12. That is to say, using the reference voltage of the reference resistor RE as shown in Figure 1 as the reference voltage can avoid introducing multiple reference circuits, which may be conducted by the body fluid, making the detection unstable. By sharing a reference circuit, it is ensured that there is only one reference potential on the entire sweat diversion channel 210 (where the sweat can reach), so that both the first detection circuit 11 and the second detection circuit 12 can operate stably, achieving a better detection effect.

[0185] The following calculates multiple detection results such as biometric values, liquid components, and component contents through the first detection signal of the first detection circuit 11 and the second detection signal of the second detection circuit 12, and details the body fluid detection method and detection results of the present invention. The biometric values include at least one of local sweating rate, whole body sweating rate, whole body sweating volume (whole body sweating water loss), whole body water balance, degree of hydration, and fatigue value. The sweat component content may include at least one of sodium ion concentration, sweat potassium ion concentration, glucose concentration, sodium ion sweating loss, potassium ion sweating loss, glucose sweating loss, sodium balance, potassium balance, etc.

[0186] Calculation of local sweating rate (such as the first excretion rate): Record the times T1, T2,..., T n when the sweat flows to A1, A2,..., A n . By adding the width a and height b of the diversion channel 210, and the distance S n -S n-1 that the sweat flows through in the diversion channel 210, the sweating rate v per unit area at the location of the detection device (such as the arm, head, back, etc.) within the unit time T n -T n-1 can be calculated, with the unit: mL / m n_water_local / h, referring to Formula 1 or Formula 24. 2 / h, referring to Formula 1 or Formula 24.

[0187]

[0188] Wherein: a is the width of the diversion channel 210, unit: m;

[0189] b is the height of the diversion channel 210, unit: m;

[0190] S n The distance from the sweat inlet of the diversion channel 210 to the A n th sweat measurement point (or the nth sensor), unit: m;

[0191] T n The total time for the sweat to reach the A n th sweat measurement point to have a reaction (for example, this total time can be the time for the sweat to flow from the sweat inlet of the diversion channel 210 to the nth sensor, causing the first state and the second state of the sensor to switch, or the time from starting the body fluid detection device to the sweat flowing to the nth sensor, causing the first state and the second state of the sensor to switch), unit: h;

[0192] S 集汗区域 represents the area of the sweat collection area of the body fluid detection device (for example, this area can be the area of the body fluid detection device covering the human skin, or the area of the collection component or the sensor substrate 21 covering the human skin, etc.), unit: m 2 ;

[0193] Calculation of the whole-body sweating rate (such as the second excretion rate): The sweating rates of different parts of the human body are different. For example, the sweating rates of the forehead and chest are much higher than those of the thighs and palms. Therefore, the contribution degrees of different parts to the whole-body sweating rate are also different. The sweating contribution rates of different parts are measured through standard experiments Then, using the contribution rate to inversely calculate the whole-body sweating rate v n_water_whole , unit: mL / m 2 / h, referring to Formula 2 or Formula 25. Therefore, this can take different values according to the position where the detection device is placed. This can be a positive number. For example, it can take values such as 0.1 - 10 or 10 - 50, etc. Of course, it can also be set or modified according to actual needs.

[0194]

[0195] Whole-body sweating sodium ion concentration: The second detection circuit 12 can use a sensor prepared based on the principle of ion-selective electrodes to detect the sodium ion concentration C of the local sweat sample in real time Na_local , unit mmol, referring to Formula 9. The whole-body sweating sodium ion concentration can be inversely calculated using the contribution rate to obtain the whole-body sweating sodium ion concentration C Na_whole , unit mmol

[0196] Potassium ion concentration in whole-body sweating: The second detection circuit 12 of the detection device can use a sensor prepared based on the principle of ion-selective electrodes to detect in real time the potassium ion concentration C in the sweat sample of the local detection area K_local , in mmol, and then use the contribution rate to inversely calculate the potassium ion concentration C in whole-body sweating K_whole , in mmol, referring to Formula 10.

[0197] Glucose concentration in whole-body sweating: The device uses a sensor prepared based on the principle that glucose oxidase catalyzes glucose to undergo an oxidation reaction to generate a microcurrent to detect in real time the glucose concentration C in the sweat of the local detection area GLU_local , in μmol, and then use the contribution rate to inversely calculate the glucose ion concentration C in whole-body sweating GLU_whole , in μmol, referring to Formula 11.

[0198] Whole-body sweating volume (whole-body sweating water loss volume): The whole-body sweating volume V can be calculated by the whole-body sweating rate and the human body surface area n waterloss , unit: mL, where the human body surface area can be calculated from height and weight, referring to Formula 3 and 4 or Formula 26 and 27;

[0199]

[0200] S BSA = 0.0061×H×0.0128M - 0.1529 (Formula 27)

[0201] T n represents the total duration of response at the nth sweat measurement point A n or the time as described above, unit: h;

[0202] S BSA represents the body surface area of the measured person, unit: m 2 ;

[0203] H represents the height of the measured person, unit: cm;

[0204] M represents the weight of the measured person, unit: kg;

[0205] Sodium ion sweating loss in whole body: Calculate the sodium ion sweating loss M in whole body through the sodium ion concentration in whole body sweat and the whole-body sweating volume Na+loss , unit: mg, referring to Formula 28;

[0206]

[0207] Total potassium ion sweating loss: Calculate the total potassium ion sweating loss M by multiplying the total body sweat potassium ion concentration by the total body sweating volume K+loss , unit: mg, refer to formula 29;

[0208]

[0209] Total glucose sweating loss: Calculate the total glucose sweating loss M by multiplying the total body sweat glucose concentration by the total body sweating volume GLU_loss , unit: mg, refer to formula 30;

[0210]

[0211] Total body water balance: The difference between total water loss and total water intake, where total loss includes sweat loss and sweat evaporation, unit: ml, combined with reference to formulas 5 - 7.

[0212] Total body sodium balance: The difference between total sodium loss and total sodium intake, where total loss includes sweat loss and sweat evaporation. Since the detection method of sodium ion concentration in sweat is limited, this algorithm ignores it, unit: mg, refer to formulas 31 - 33;

[0213] BAL n Na = TotalM Naloss - TotalM Naintake (Formula 31)

[0214] Total M Naloss = M nNaloss (Formula 32)

[0215]

[0216] Where: n represents the number of times of fluid intake, including before exercise, during exercise, and after exercise, unit: ml;

[0217] P nNa1 represents the percentage of ionic sweat in the fluid, relying on the value saved in the previous exercise input by the user or recorded by the system, mg;

[0218] Total body potassium balance: The difference between total potassium loss and total potassium intake, where total loss includes sweat loss and sweat evaporation. Since the detection method of potassium ion concentration in sweat is limited, this algorithm ignores it, unit: mg, combined with reference to formulas 34 - 36;

[0219] BAL n K = TotalM Kloss - TotalM K-intake (Formula 34)

[0220] TotalM Kloss = MnKloss (Formula 35)

[0221]

[0222] Where: n represents the number of times of sweat intake, including before exercise, during exercise, and after exercise, unit: ml;

[0223] P nK represents the percentage of ionic sweat in the liquid, relying on the value saved in the previous exercise input by the user or recorded by the system, mg;

[0224] Calculation of hydration level: The percentage of the total mass of water loss in the total body weight, referring to Formula 8;

[0225] Calculation of exercise fatigue value: An algorithm framework can be adopted: weighted by the proportion of the peak interval time of TRIMP. The weighting value can adopt a score interval: 0-21. The score period can be divided into several levels. For example, it is divided into four levels as shown below. The fatigue level of the user can be obtained according to the fatigue value calculated as follows, so as to estimate the degree of exercise that oneself can do. The fatigue levels can include: Light (0-9.9); Moderate (10-13.9); Strenuous (14-17.9); AllOut (18-21). The user can control their exercise amount with reference to the fatigue level. If the fatigue value is 5, then the user's level is Light (0-9.9).

[0226] The fatigue value can be calculated through the contribution index of the fatigue value, the contribution index weight rate, the peak interval, the peak interval contribution weight rate, the proportion of the peak interval time, etc. The fatigue value includes at least one of the fatigue value of a single index, the overall fatigue value of a single exercise, or the overall fatigue value of multiple exercises in a day. The fatigue value of a single index can refer to the fatigue value at a certain time point T n of the fatigue value.

[0227] Among them, the contribution index index of the fatigue value can include:

[0228] Inde1 is the local sweating rate (the first excretion rate) (v n_water_local )

[0229] Index2 is the local sodium ion concentration (sample sodium ion concentration) (C Na-whole )

[0230] Index3 is the local sweat sugar concentration (sample sweat sugar concentration) (C GLU-whole )

[0231] The contribution index weight rate β can include:

[0232] β Index1= 40%

[0233] β Index2 = 20%

[0234] β Index3 = 40%

[0235] The peak interval may include:

[0236] T Extent1 : 50% - 59%

[0237] T Extent2 : 60% - 69%

[0238] T Extent3 : 70% - 79%

[0239] T Extent4 : 80% - 89%

[0240] T Extent5 : 90% - 100%

[0241] The contribution weight ratio γ of the peak interval may include:

[0242] γ Extent1 = 0.1

[0243] γ Extent2 = 0.1

[0244] γ Extent3 = 0.2

[0245] γ Extent4 = 0.2

[0246] γ Extent5 = 0.4

[0247] The peak interval time ratio PoT can be calculated through time and the peak period at that time, and can refer to Formula 21:

[0248] The fatigue value Fatigue of a single index indexm (Current fatigue value) can be calculated through the peak interval time ratio and the peak interval contribution weight ratio, and can refer to Formula 37:

[0249]

[0250] The overall fatigue value Fatigue (single - time fatigue value) of a single exercise can be calculated through the fatigue value of a single index and the contribution index weight ratio, and can refer to Formula 38:

[0251]

[0252] The overall fatigue value algorithm for exercising multiple times a day: Integrate the time of multiple exercises and regard it as one exercise for interval weighting. The calculation process can refer to Formula 38.

[0253] The calculation formulas and methods for the sweat emission rate, discharge amount, composition, and composition content as described above can be applied to calculate tears or saliva, and no separate description of tears or saliva will be given here.

[0254] In summary, the sweat detection device of the present invention can obtain a first detection signal through the first detection circuit 11 and the reference circuit, thereby obtaining the discharge rate and discharge amount of the body fluid, and further detecting the discharge rate and discharge amount of the body fluid of the human body, facilitating users and medical staff to monitor the degree of body fluid loss in the human body and replenish body fluid in the case of excessive body fluid loss. In addition, the composition of the body fluid can be detected through the second detection circuit 12, and the composition of the body fluid can be used to calculate the content of the composition, etc., so as to monitor the amount and content of the composition in the body fluid by users and medical staff. When a certain component is missing, or the content is excessive or too little, operations such as content control can be carried out in a timely manner. For example, when sodium ions or potassium ions are severely lost, sodium ions or potassium ions can be replenished.

[0255] In the description of the present application, it should be understood that the terms "first" and "second" are only used for descriptive purposes and cannot be understood as indicating or implying relative importance or implicitly specifying the quantity of the indicated technical features. Thus, the features defined with "first" and "second" may explicitly or implicitly include one or more of the said features. In the description of the present application, "a plurality" means two or more, unless otherwise specifically defined.

[0256] In the description of the method process of the present application, the corresponding step numbers "Step S1", "Step S2", etc. and "Combination 1", "Combination 2", etc. are only used to distinguish the different contents of each step or combination, and cannot be understood as indicating or implying that the steps or combinations must be in numerical order. Unless otherwise specifically defined, the steps or combinations can be reordered during actual operation.

[0257] It should be noted that unless otherwise clearly defined and limited, the terms "installed", "connected", and "connected" should be understood in a broad sense. For example, it can be a fixed connection, a detachable connection, or an integral connection; it can be a mechanical connection, an electrical connection, or a connection that can communicate with each other; it can be directly connected, or indirectly connected through an intermediate medium, and can be the connection inside two components or the interaction relationship between two components. For those of ordinary skill in the art, the specific meanings of the above terms in the present application can be understood according to specific circumstances.

[0258] Those skilled in the art can make various corresponding changes and deformations according to the technical solutions and concepts described above, and all such changes and deformations should fall within the protection scope of the claims of the present invention.

Claims

1. A body fluid detection method, characterized in that, Including the following steps: Obtain a body fluid sample; Detect the body fluid sample and generate a first detection signal; wherein, multiple detection points are included to detect the body fluid sample; The first detection signal is used to generate a biometric value; wherein, the biometric value includes the excretion rate of the body fluid; the process of detecting the body fluid sample and generating the first detection signal includes the following steps: Detect the body fluid sample through at least one sensor, and switch the first state and the second state of at least one of the sensors; When the body fluid sample reaches each detection point, it is electrically connected to the corresponding sensor; The sensor in contact with the body fluid sample switches between the first state and the second state; Based on the switching times of the first state and the second state of each of the sensors, the sampling circuit generates one or more first detection signals, or the sampling circuit generates one or more first detection signals according to the combination manner of the first state and the second state of each sensor; the discharge rate of the body fluid includes a first discharge rate, and the calculation formula of the first discharge rate is: , where n is the number of sensors, Tn represents the first detection signal, that is, the time when the nth sensor contacts the body fluid sample, Vn represents the volume of the body fluid sample when it reaches the nth sensor, K is a constant, and S 局部 represents the area of the region for obtaining the body fluid sample; The body fluid sample further includes a second excretion rate, and the calculation formula of the second excretion rate is: ， wherein is the contribution rate of the body fluid sample.

2. The body fluid detection method according to claim 1, characterized in that The first detection signal changes with the time of switching between the first state and the second state of each sensor, or the first detection signal changes with the change of the combination mode of the first state and the second state of the sensor.

3. The body fluid detection method according to claim 1 or 2, characterized in that: The process of detecting the body fluid sample and generating the first detection signal further includes the following steps: The body fluid sample sequentially passes through the detection points along a predetermined order; Each detection point corresponds to a detection electrode of a sensor. When the body fluid sample reaches the detection electrode corresponding to the detection point, it contacts the sensor; When the body fluid sample reaches the electrode corresponding to the detection point, the connection relationship between the sensor connected to the electrode and the reference circuit changes.

4. The body fluid detection method according to claim 3, characterized in that: The ways in which the connection relationship between the sensor and the reference circuit changes include: changing from conducting to disconnecting or short-circuiting, or from disconnecting to conducting or short-circuiting, or from short-circuiting to conducting or disconnecting.

5. The body fluid detection method according to claim 1 or 2, characterized in that It further includes the following steps: The body fluid collection component diverts the body fluid sample to the second detection circuit; After the second detection circuit contacts the body fluid sample, it generates a second detection signal, and the second detection signal is used to calculate the component content of the body fluid. The second detection signal includes the sample components and the sample component content.

6. The body fluid detection method according to claim 5, wherein It further includes the following steps: the excretion rate of the body fluid and / or at least part of the component content of the body fluid are used to calculate the fatigue value, and the fatigue value includes the current fatigue value, single fatigue and overall fatigue value.

7. The body fluid detection method according to claim 6, characterized in that, The calculation process of the current fatigue value includes: Obtain the body fluid excretion rate, sample sodium ion concentration, and sample sweat sugar concentration as contribution indicators; Obtain the contribution index weight rate, peak interval, and peak interval contribution weight rate; Calculate the proportion of the peak interval time according to the current time and the peak interval at which the time is located; Calculate the current fatigue value according to the proportion of the peak interval time and the peak interval contribution weight rate.

8. The body fluid detection method according to claim 7, characterized in that, The calculation process of the single fatigue value includes: obtaining the contribution index weight rate and at least one current fatigue value to calculate the single fatigue value.

9. A body fluid detection device, characterized in that, This body fluid detection device uses the body fluid detection method described in any one of claims 1-8 for detection; It includes a body fluid collection component and a body fluid detection component; The body fluid collection component is used to obtain a body fluid sample; The body fluid detection component is used to detect a body fluid sample and generate the first detection signal; the first detection signal is used to generate a biometric value; wherein, the biometric value includes the excretion rate of the body fluid; the process of detecting the body fluid sample and generating the first detection signal includes the following steps: Detect the body fluid sample through at least one sensor, and switch the first state and the second state of at least one of the sensors; When the body fluid sample reaches each detection point, it is electrically connected to the corresponding sensor; The sensor in contact with the body fluid sample switches between the first state and the second state; According to the switching time of the first state and the second state of each sensor, the sampling circuit generates one or more first detection signals, or according to the combination mode of the first state and the second state of each sensor, the sampling circuit generates one or more first detection signals; The excretion rate of the body fluid includes a first excretion rate, and the calculation formula of the first excretion rate is: ， where n is the number of sensors, Tn represents the first detection signal, that is, the time when the nth sensor contacts the body fluid sample, Vn represents the volume of the body fluid sample when it reaches the nth sensor, K is a constant, and S 局部 represents the area of the region for obtaining the body fluid sample; The body fluid sample further includes a second excretion rate, and the calculation formula of the second excretion rate is: ， Among them is the contribution rate of the body fluid sample.

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