Physiological parameter acquisition equipment

Abstract

The utility model relates to the technical field of medical instruments, and provides physiological parameter acquisition equipment which comprises a host, a wrist strap, a pulse signal acquisition device, a metabolic heat detection component, an infrared spectrum detection device and a control device, the pulse signal acquisition device is mounted on the wrist strap and is used for acquiring a pulse signal of a to-be-tested person; the metabolic heat detection device is used for collecting metabolic data of a person to be detected, and the infrared spectrum detection device is used for collecting near-infrared diffuse reflection signals of a target part of the person to be detected. The problems that a physiological parameter health monitor is single in function and poor in integration are solved.

Description

Technical Field

[0001] The utility model relates to the technical field of medical devices, in particular to a physiological parameter acquisition device. Background Art

[0002] With the continuous development of modern medical technology, physiological parameter health monitors have become an indispensable health management tool in people's daily lives. However, the physiological parameter health monitors currently widely used in the market have relatively simple functions. For example, oximeters for monitoring blood oxygen concentration and blood oxygen saturation, blood pressure monitors for monitoring heart rate and blood pressure, etc., lack integrated physiological parameter acquisition equipment. At the same time, when facing the prevention and management of chronic diseases such as diabetes, users usually need to use blood glucose meters in addition to blood glucose measurement through invasive needle-drawing methods. This not only increases the user's usage cost and inconvenience, but may also cause user discomfort and resistance due to frequent invasive operations.

[0003] In view of this, a physiological parameter acquisition device and a physiological parameter acquisition method are provided to solve the problems in the prior art of single function and poor integration of physiological parameter health monitors. Utility Model Content

[0004] The utility model provides a physiological parameter acquisition device and a physiological parameter acquisition method to solve the problems of single function and poor integration of physiological parameter health monitors in the prior art, thereby achieving the integration of physiological parameter acquisition.

[0005] The utility model provides a physiological parameter acquisition device, comprising:

[0006] A host, the host comprising a housing having a plurality of finger grooves formed therein, an air pump mounted within the housing, a metabolic heat detection assembly for collecting metabolic data of a subject, and an infrared spectrum detection device for collecting near-infrared diffuse reflectance signals from a target area of ​​the subject, the metabolic heat detection assembly and the infrared spectrum detection device being disposed within the finger grooves;

[0007] A wristband, which is used to be put on the wrist of the person to be tested;

[0008] A pulse signal acquisition device, which is mounted on the wristband and acquires the pulse signal of the person being measured;

[0009] The pulse signal acquisition device comprises:

[0010] An airbag assembly, the airbag assembly being installed in the wristband and being in communication with the air pump;

[0011] A pulse pressure sensor, the pulse pressure sensor is used to collect the current pressure value of the airbag assembly;

[0012] an air pump, connected to the airbag assembly and configured to inflate the airbag assembly;

[0013] Both the host and the wristband are provided with an air pump interface, which is connected to the air pump interface on the host through a pneumatic pipe. Both the host and the wristband are provided with a data cable interface, which is connected to the data cable interface on the host through a data cable.

[0014] In some embodiments, the pneumatic conduit is a hose.

[0015] In some embodiments, the airbag assembly includes at least two airbags, each of which is stacked along the radial direction of the wristband.

[0016] In some embodiments, the airbag assemblies are in at least three groups, and each of the airbag assemblies is arranged along a tangential direction of the wristband.

[0017] In some embodiments, the metabolic heat detection component includes a temperature sensor,

[0018] Infrared sensors, humidity sensors and optical measuring devices.

[0019] In some embodiments, there are four finger grooves.

[0020] In some embodiments, a charging port, a power button, and a display screen are provided on the housing of the host.

[0021] In some embodiments, the shell is made of TPU material.

[0022] The physiological parameter acquisition device provided by the present invention includes a host and a wristband, the host includes a shell, an air pump is installed in the shell, a metabolic heat detection component for acquiring metabolic data of the subject to be tested, and an infrared spectrum detection device for acquiring near-infrared diffuse reflection signals of the target part of the subject to be tested is installed on the shell; the wristband is used to be sleeved on the wrist of the subject to be tested; a pulse signal acquisition device, the pulse signal acquisition device is installed in the wristband, and obtains the pulse signal of the subject to be tested; the pulse signal acquisition device includes an airbag assembly, a pulse pressure sensor and an air pump, the airbag assembly is installed in the wristband, and the airbag assembly is connected to the air pump; the pulse pressure sensor is used to acquire the current pressure value of the airbag assembly; an air pump interface is provided on both the host and the wristband, and the air pump interface on the host is connected to the air pump interface on the wristband through a pneumatic pipeline, and a data line interface is provided on both the host and the wristband, and the data line interface on the host is connected to the data line interface on the wristband through a data line.

[0023] Thus, the physiological parameter acquisition device provided by this utility model integrates a pulse signal acquisition device, a metabolic heat detection device, and an infrared spectrum detection device into a wristband, thereby enabling the acquisition of pulse signals, metabolic data, and near-infrared diffuse reflectance signals, and further enabling the generation of visualizations of pulse, metabolic data, and blood glucose concentration values. This solves the problem of single-function and poor integration of physiological parameter health monitors in the prior art, thereby achieving integrated physiological parameter acquisition. BRIEF DESCRIPTION OF THE DRAWINGS

[0024] In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the following is a brief introduction to the drawings required for use in the embodiments or the description of the prior art. Obviously, the drawings described below are some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without paying any creative work.

[0025] Figure 1 This is a schematic structural diagram of a physiological parameter acquisition device provided by the present invention;

[0026] Figure 2 yes Figure 1 A cross-sectional view of a cuff in the physiological parameter acquisition device shown;

[0027] Figure 3 for Figure 1 A partial enlarged view of the host computer in the physiological parameter acquisition device shown;

[0028] Figure 4 Schematic diagram of the correspondence between the amplitude parameter and the time parameter of the pulse wave time domain waveform;

[0029] Figure 5 Schematic diagram of the angle characteristics of the pulse time domain waveform;

[0030] Figure 6 This is a control flow chart of the pulse signal acquisition device provided by the present invention;

[0031] Figure 7 is a schematic diagram of blood glucose level calculation dimensions provided by the present invention;

[0032] Figure 8 It is a structural schematic diagram of the infrared spectrum detection device provided by the present invention;

[0033] Figure 9 This is a flow chart of the physiological parameter acquisition method provided by the present invention.

[0034] Reference numerals:

[0035] 100-the wrist of the person being tested;

[0036] 11-housing, 12-hose, 13-data cable, 14-charging port, 15-power button, 16-display, 17-air pump interface, 18-finger groove;

[0037] 2-Wristband;

[0038] 21-airbag, 22-pulse pressure sensor;

[0039] 3-Metabolic heat detection component;

[0040] 4-Infrared spectrum detection device. DETAILED DESCRIPTION

[0041] The following embodiments of the present invention are described in further detail with reference to the accompanying drawings and examples. The following examples are used to illustrate the present invention, but are not intended to limit the scope of the present invention.

[0042] In the description of the embodiments of the present invention, it should be noted that the terms "center", "longitudinal", "lateral", "upper", "lower", "front", "back", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", etc., indicating the orientation or positional relationship, are based on the orientation or positional relationship shown in the accompanying drawings, and are only for the convenience of describing the embodiments of the present invention and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, be constructed and operate in a specific orientation, and therefore should not be understood as limiting the embodiments of the present invention. In addition, the terms "first", "second", and "third" are used for descriptive purposes only and should not be understood as indicating or implying relative importance.

[0043] In the description of the embodiments of the present invention, it should be noted that, unless otherwise specified or limited, the terms "connected" and "connection" should be understood in a broad sense. For example, they can refer to fixed connections, detachable connections, or integral connections; mechanical connections, electrical connections; direct connections, or indirect connections through an intermediary. Those skilled in the art will understand the specific meanings of the above terms in the embodiments of the present invention based on specific circumstances.

[0044] In the embodiments of the present invention, unless otherwise expressly specified or limited, a first feature being "above" or "below" a second feature may mean that the first and second features are in direct contact, or that the first and second features are in indirect contact through an intermediate medium. Furthermore, a first feature being "above," "above," or "above" a second feature may mean that the first feature is directly above or diagonally above the second feature, or simply means that the first feature is higher in level than the second feature. A first feature being "below," "below," or "below" a second feature may mean that the first feature is directly below or diagonally below the second feature, or simply means that the first feature is lower in level than the second feature.

[0045] In the description of this specification, the description with reference to the terms "one embodiment", "some embodiments", "example", "specific example", or "some examples" means that the specific features, structures, materials or characteristics described in conjunction with the embodiment or example are included in at least one embodiment or example of the embodiment of the utility model. In this specification, the schematic representation of the above terms does not necessarily refer to the same embodiment or example. Moreover, the specific features, structures, materials or characteristics described can be combined in any one or more embodiments or examples in a suitable manner. In addition, those skilled in the art can combine and combine different embodiments or examples described in this specification and the features of different embodiments or examples without contradiction.

[0046] To address the limitations of existing physiological parameter health monitors, which suffer from limited functionality, invasive blood glucose measurement, and inconvenient operation, this invention proposes a multifunctional physiological parameter acquisition device that integrates noninvasive blood glucose measurement technology with flexible pulse sensing technology. This device utilizes a single device to achieve noninvasive blood glucose measurement while simultaneously monitoring multiple physiological health parameters, such as blood pressure and pulse, using flexible pulse sensing technology. Furthermore, this technology synchronizes monitoring data to a mobile app through a real-time feedback transmission mechanism, enabling users to monitor their physiological health status in real time.

[0047] Combine Figure 1 and Figure 2 According to an embodiment of the present invention, the physiological parameter acquisition device includes a host, a wristband 2, a pulse signal acquisition device, a metabolic heat detection component, an infrared spectrum detection device, and a control device; the wristband 2 is used to be mounted on the wrist 100 of the subject to be tested, and the wristband 2 is a flexible belt, for example, it can be in the form of a blood pressure wristband 2; the host and the wristband 2 are both provided with an air pump interface 17, and the air pump interface 17 on the host is connected to the air pump interface 17 on the wristband 2 through a hose 12, and the host and the wristband 2 are both provided with a data line interface, and the data line interface on the host is connected to the data line interface on the wristband 2 through a data line 13. The pulse signal acquisition device is installed on the wristband 2 and obtains the pulse signal of the subject to be tested, the metabolic heat detection component is installed on the host and collects the metabolic data of the subject to be tested; the infrared spectrum detection device is installed on the host and collects the near-infrared diffuse reflection signal of the target part of the subject to be tested. The control device is used to receive the pulse signal, the metabolic data and the near-infrared diffuse reflection signal, and generate a blood glucose concentration value based on the near-infrared diffuse reflection signal; the control device is also used to generate a visualized physiological parameter collection result from the pulse signal, the metabolic data and the blood glucose concentration value.

[0048] The main unit has a housing 11, which can be made of TPU. A micro air pump and electromagnetic air release valve are installed inside the housing 11. These control the inflation and deflation of the airbag 21 in the pulse signal acquisition device based on real-time data feedback from the air pressure sensor. The housing 11 also includes a charging port 14, a power button 15, and a display 16. Display 16 can be a color liquid crystal display (LCD) with high resolution and a wide viewing angle to ensure clear display at different angles. It monitors and displays physiological health parameters in real time, providing data graphs or trend charts to help users intuitively understand the changing trends of physiological parameters.

[0049] Furthermore, a finger groove 18 is provided on the housing 11 of the host. In this embodiment, four groups of finger grooves 18 can be provided, and each sensor or sensor probe (such as an infrared sensor 41, a laser diode array 42 or a photoelectric receiver 43, a temperature sensor probe, etc.) is provided in the finger groove 18.

[0050] The pulse signal acquisition device is used to collect information such as the blood pressure and pulse of the person to be measured. In some embodiments, the pulse signal acquisition device provided by the present invention includes an airbag assembly, a pulse pressure sensor 22 and an air pump; wherein the airbag assembly is installed in the wristband 2, and the airbag assembly is connected to the air pump; the pressure control of the floating, middle and sinking pulse patterns of traditional Chinese medicine pulse diagnosis can be achieved by using an inflatable airbag pressure method, thereby completing the pulse signal acquisition at the inch, guan and chi positions of the wrist. The pulse pressure sensor 22 is used to collect the current pressure value of the airbag assembly, and the control device generates a start instruction or a stop instruction based on the relationship between the current pressure value and the pressure threshold; the pulse pressure sensor 22 is used as a pulse signal acquisition device to detect the pressure changes generated when the artery pulsates and convert them into electrical signals. According to the way of collecting signals, pulse sensors can be divided into piezoelectric, piezoresistive and photoelectric types; piezoelectric and piezoresistive sensors convert the pressure process of the pulse beating into signal output through micro-pressure materials (such as piezoelectric sheets, bridges, etc.), and photoelectric pulse sensors can be divided into piezoelectric, piezoresistive and photoelectric types. The sensor converts the signal by detecting the change in the transmittance of the blood vessels during the pulse beating process; the air pump starts in response to the start instruction issued by the control device, or shuts down in response to the stop instruction issued by the control device; for example, the start instruction or stop instruction of the air pump is generated in response to the user's operation, and the corresponding instruction of the air pump can also be generated according to the current pressure value of the airbag 21 detected and the relationship between the current pressure value and the pressure threshold, that is, if the current pressure value is less than the pressure threshold, the start instruction of the air pump is generated, and if the current pressure value is greater than the pressure threshold, the stop instruction of the air pump is generated.

[0051] In some embodiments, the pulse signal acquisition device is specifically a flexible pulse sensor array. That is, a flexible pulse pressure sensor 22 is located inside the ring-shaped wristband 2 to detect the pulse signal when the airbag 21 is pressurized. The detection signal is transmitted back in real time via the aforementioned data transmission line for signal conditioning and data processing in the host computer. The flexible pulse pressure sensor 22 captures the pulse signal generated during the pressurization of the airbag 21. These signals are inevitably mixed with noise and other interference. To improve signal clarity, signal conditioning is required. For example, a wavelet noise reduction algorithm can be used to effectively remove noise and baseline drift, making the signal cleaner. The conditioned signal is converted to a digital signal via an analog-to-digital converter (ADC) for subsequent computer processing. In this embodiment, the peak points of the pulse wave at the radial artery of the wrist can be used as a reference to calculate the time intervals between adjacent peak points to obtain the heart rate. Heart rate data is an important basis for heart rate variability analysis. In addition, a software algorithm can be used to extract the respiratory wave from the pulse wave signal and calculate the number of respiratory waves per unit time to obtain the respiratory frequency.

[0052] Specifically, the pulse wave waveform characteristics and their changes are not only the basis for TCM pulse identification, but also reflect the operating status of the human cardiovascular system and contain a large amount of physiological and pathological information. In this embodiment, multiple time domain characteristics of the pulse wave are extracted, and each feature point of the pulse wave time domain waveform is extracted by the extreme value method and the amplitude parameter and time parameter of each point are obtained, thereby calculating the amplitude ratio and time ratio of the pulse wave. Among them, the corresponding situation of the amplitude parameter and time parameter of the pulse wave time domain waveform is as follows: Figure 4 As shown; Figure 4Among them, h1 refers to the main wave amplitude, which is the height from the main wave peak to the pulse wave baseline, mainly reflecting the ejection function of the left ventricle and the compliance of the large arteries. When the left ventricular contraction force is strong and the compliance of the large arteries is good, h1 is high, otherwise it is small; h2 refers to the amplitude of the pre-dicrotic wave, which is the height from the pre-dicrotic wave peak to the pulse wave baseline, mainly reflecting the elasticity of the arterial blood vessels and the peripheral resistance state; h3 refers to the amplitude of the descending gorge, which is the height from the bottom of the descending gorge to the pulse wave baseline. The height of the descending gorge corresponds to the diastolic pressure and is mainly related to the peripheral resistance of the arterial blood vessels and the closure function of the aortic valve. As the peripheral resistance increases, h3 increases, and vice versa. h4 refers to the amplitude of the dicrotic wave. h4 is the height between the peak of the dicrotic wave and the baseline parallel line at the bottom of the descending mid-valve. The amplitude of the dicrotic wave mainly reflects the elasticity (compliance) of the large arteries and the function of the aortic valve. When the compliance of the large arteries decreases, h4 decreases, or when the aortic valve is sclerotic or insufficient, h4 can be 0 or even a negative value. t1 is the time value from the starting point of the pulse graph to the main wave peak, corresponding to the rapid ejection phase of the left ventricle; t2 is the time value between the starting point of the pulse graph and the descending mid-valve, corresponding to the contraction phase of the left ventricle; t3 is the time value between the descending mid-valve and the end point of the pulse graph, corresponding to the diastole phase of the left ventricle; t is the time value between the starting point and the end point of the pulse graph, corresponding to the cardiac cycle (pulsation cycle) of the left ventricle.

[0053] To better reflect pulse characteristics and cardiovascular status, pulse analysis is generally performed using relative values ​​of various parameters. The h2 / h1 ratio primarily reflects vascular wall compliance and peripheral resistance. Poor vascular compliance and a rapid reentry of the peripheral reflected wave result in an early pre-dicrotic wave. Increased h2 / h1 results in an obtuse pre-dicrotic wave angle. Elevated h2 / h1, even exceeding 1, and an acute pre-dicrotic wave angle indicate high vascular tone and good zero-pressure compliance, a phenomenon often seen in tight pulses stimulated by various factors. This ratio is crucial for pulse diagnosis in Traditional Chinese Medicine. h3 / h1 primarily reflects the level of peripheral resistance. When peripheral vasoconstriction occurs, resistance increases, and h3 / h1 rises. Conversely, when peripheral resistance decreases, h3 / h1 decreases, which is often seen in cases of qi deficiency and blood deficiency in TCM. h4 / h1 primarily reflects aortic compliance and aortic valve function. When arterial compliance is poor or aortic valve regurgitation is incomplete, h4 / h1 is equal to 0 or even negative. Conversely, when the aortic valve function is normal, arterial compliance is good, and blood volume is replete, h4 / h1 increases. t1 / t is related to cardiac ejection function. When left ventricular systolic function is impaired and ejection rate decreases, t1 / t is prolonged. (t2-t1) / t is also related to cardiac ejection function. When cardiac output decreases, (t2-t1) / t decreases. t2 / t3 is related to heart rate. When the heart rate accelerates, t2 / t3 is greater than 1, which is often seen in cases of yin deficiency and hyperactivity of fire in TCM.

[0054] Angular features such as Figure 5As shown in Figure 1, A1, A2, A3, A4, and A5 represent the five angle features of the pulse wave. A1 and A2 represent the slopes of the rising and falling branches of the main pulse wave, respectively; A3 and A4 represent the rising and falling slopes of the tidal wave; and A5 represents the rising slope of the dicrotic wave. In the pulse wave time-domain analysis, statistical analysis was performed on several key waveform features in patients with CHD and healthy subjects, including h2 / h1, h3 / h1, t1 / T, t2 / T, t3 / T, A2, and A3. As shown in Table 1, the statistical analysis of these feature data yielded the mean and standard deviation of the corresponding features in patients with CHD and healthy subjects. The amplitude ratio of the tidal wave to the main wave in patients with CHD was significantly greater than that in healthy subjects, indicating that the amplitudes of the main wave and tidal wave in patients with CHD are closer. At the same time, the slope A2 of the descending branch of the main pulse wave and the rising slope A3 of the tidal wave of patients with coronary heart disease are greater than the angular characteristic values ​​of the pulse wave of normal people, reflecting that due to arteriosclerosis, the elasticity and flexibility of blood vessels in patients with coronary heart disease are reduced. When entering the stage of slowed ejection, the elastic retraction ability of the dilated blood vessels is weakened.

[0055] Table 1 Comparison of pulse parameters between coronary heart disease and normal subjects

[0056]

[0057] In a specific use case, feature extraction and selection are first performed. Based on the characteristics and physiological significance of the pulse signal, appropriate time-domain features are selected, including the seven typical features of the pulse wave, the amplitude ratio and time ratio between feature points, the pulse wave period T, and five angle features. Feature values ​​are automatically extracted using image processing or signal processing algorithms. Comparative analysis is then performed, specifically including the following steps:

[0058] Obtain normal data: obtain the average value and standard deviation of normal people's pulse waveform characteristic data from literature or database;

[0059] Comparing characteristic values: Compare the user's characteristic value with the average characteristic data of normal people and calculate the difference value; for example: difference value = user characteristic value - average characteristic value of normal people, standardized difference value = (difference value - standard deviation of characteristic value of normal people) / (standard deviation of characteristic value of normal people);

[0060] Abnormality judgment: Based on the size and direction of the difference, it is judged whether the user's pulse waveform is abnormal. If the difference value is greater than the normal range or the standardized difference value is greater than the threshold, it is considered abnormal.

[0061] Based on the comparison results obtained in the previous step, the health status assessment is performed, including:

[0062] Combined with physiological significance: Combined with the waveform characteristics of the pulse graph (such as amplitude, time parameters, etc.), the user's health status is assessed;

[0063] Reference to other indicators: Combine pulse wave characteristics with other physiological indicators (such as blood pressure, heart rate, blood lipids, etc.) for comprehensive evaluation.

[0064] Finally, a report is generated and recommendations are provided based on the health status assessment results. Specifically, based on the analysis results, a report is generated containing information such as the user's pulse waveform characteristics, differences from normal people, and health assessment results. Based on the assessment results, corresponding health recommendations are provided, such as diet, exercise, and drug treatment.

[0065] In some embodiments, please refer to Figure 1 and Figure 2 The airbag assembly includes at least two airbags 21, each of which is stacked along the radial direction of the wristband 2. In other words, the airbag assembly can be arranged in an array, with two airbags 21 arranged sequentially from the outside to the inside along the radial direction of the ring-shaped wristband 2. Two airbags 21 constitute one airbag assembly. It should be noted that the number of airbag assemblies is two, which is only a specific arrangement and can be adjusted in actual applications to suit specific applications. Each airbag assembly contains multiple interconnected airbags 21. After being filled with an appropriate amount of air, the pulse sensor can be pressed against the wrist with stable pressure. These airbags 21 are stacked to ensure that the center and edge of each airbag 21 are roughly the same size, so that each detection point on the pulse sensor is subjected to uniform pressure.

[0066] Furthermore, the airbag assembly is composed of at least three groups, and each of the airbag assemblies is arranged along the tangential direction of the wristband 2. The three airbag combinations are arranged along the tangential direction of the ring-shaped wristband 2, corresponding to the three key parts of the patient's pulse, namely, Chi, Guan, and Cun. As the core means of pressurization in pulse diagnosis technology, the airbag array ensures that appropriate pressure is applied during the pulse diagnosis process through a precise control mechanism. To achieve this goal, an air pressure sensor is introduced to monitor the pressure changes of each airbag 21 in real time. Based on the data fed back by the air pressure sensor, the system can control the inflation and deflation of the airbag 21.

[0067] like Figure 2 As shown, two airbags 21 are sequentially arranged along the radial direction of the ring wristband 2 from the outside to the inside. Two or more airbags 21 form an airbag combination. By applying pressure to the pulse pressure sensor 22 through the airbag combination, the size difference between the middle and edge parts of the airbag 21 can be reduced, and the entire array sensor is pressed against the surface of the wrist, so that the pressure of the airbag 21 on different points of the array sensor is consistent. In actual application, uniform pressure is achieved by uniformly inflating the airbags 21, gradually increasing the pressure on the array sensor, thereby stably collecting pulse wave information. Figure 3As shown, during the process of inflation and deflation of the airbag 21, automatic control can be achieved through pressure regulation. When the pressure sensor detects that the pressure of the airbag 21 is lower than the minimum threshold, the air pump is turned on to inflate the airbag 21. The pressure of the airbag 21 is monitored in real time during the inflation process of the airbag 21, and the air pump is controlled to stop working after the pressure of the airbag 21 reaches a preset value. When the measurement is completed, the electromagnetic relief valve is started to deflate the airbag 21.

[0068] In some embodiments, as Figure 3 The metabolic heat detection component shown includes:

[0069] The temperature sensor is a thermistor provided in the main unit, and the thermistor detection head 3 is provided inside the finger groove and is used to collect the body temperature data of the person to be measured;

[0070] An infrared sensor is installed in the finger groove and is used to collect the skin surface temperature of the person to be measured;

[0071] A humidity sensor is installed in a humidity measurement cavity provided on the host computer and is used to collect surface humidity data of the subject;

[0072] The optical measuring device includes a laser diode array and a photoelectric receiver installed in the finger groove, and is used to collect the blood oxygen saturation of the person to be measured.

[0073] Theoretically, maintaining homeostasis depends on physiological rhythms, which are determined by the interplay between metabolic heat generation, local oxygen supply, and blood glucose concentration. In the human body, glucose and oxygen from the blood are transported to cells throughout the body via the circulatory system. Within these cells, glucose is oxidized and ultimately converted into water, carbon dioxide, and energy, which is released into the surrounding environment through convection, radiation, and evaporation. The amount of heat generated by human metabolism is directly proportional to blood glucose concentration and oxygen supply and can be considered a function of these two factors. To monitor this process, the metabolic heat detection module utilizes temperature sensors, infrared sensors, humidity sensors, and optical measurement devices to convert metabolic heat-related information on temperature, humidity, blood flow rate, and oxygen saturation into data that ultimately reflects blood glucose concentration.

[0074] like Figure 7As shown, theoretically, the temperature sensor is used to collect the skin surface temperature and ambient temperature of the subject to be tested, and the radiation heat dissipation level and the convection heat dissipation level can be obtained based on the skin surface temperature and the ambient temperature; the humidity sensor is used to collect the humidity near the skin of the subject to be tested and the ambient humidity, and the evaporative heat dissipation level can be obtained based on the humidity near the skin and the ambient humidity; the blood flow rate is obtained based on the skin surface temperature, the temperature of the metal rod near the skin end, and the temperature of the metal rod far from the skin end; the optical measuring device can obtain the blood oxygen saturation; the blood glucose level can be obtained based on the radiation heat dissipation level, the convection heat dissipation level, the evaporative heat dissipation level, the blood flow rate, and the blood oxygen saturation.

[0075] The physiological rhythm of homeostasis depends on the interrelationship between metabolic heat, local oxygen supply, and blood glucose concentration. Glucose and oxygen in the blood are supplied to cells throughout the body through the circulatory system. Glucose is ultimately oxidized into water, carbon dioxide, and energy, which is dissipated to the surrounding environment through convection, radiation, and evaporation. The heat generated by human metabolism is a function of blood glucose concentration and oxygen supply, and is positively correlated with these two factors.

[0076] The principle and algorithm for calculating blood sugar levels based on radiation heat dissipation level, convection heat dissipation level, evaporative heat dissipation level, blood flow rate, and blood oxygen saturation are as follows:

[0077] According to the metabolic heat integration theory, blood glucose concentration can be estimated by the heat generated by metabolism, blood flow rate, and blood oxygen saturation. Within the normal physiological range, the relationship between them can be expressed as a linear relationship, namely:

[0078] G=a0+a1×H+a2×BF+a3×O

[0079] Among them, G is the blood glucose concentration, H is the heat generated by metabolism, BF is the blood flow rate, and O is the blood oxygen saturation.

[0080] Since the heat generated by metabolism is estimated through radiation, convection and evaporation, it can be divided into three terms, so the formula is transformed into:

[0081] G=a0+a1×R+a2×C+a3×E+a4×BF+a5×O

[0082] Among them, R is the radiation heat dissipation, C is the convection heat transfer, and E is the evaporative heat dissipation.

[0083] According to the data collected by the sensor, the radiation heat dissipation parameters, convection heat dissipation parameters, evaporation heat dissipation parameters, blood flow rate parameters and blood oxygen saturation parameters are calculated respectively. After normalizing these parameters, the coefficient a in the formula is determined by partial least squares regression analysis. i During measurement, the collected raw data are normalized and the actual blood glucose concentration can be estimated using partial least squares discriminant analysis.

[0084] Obtaining heat generated by human metabolism includes:

[0085] 1. Radiation generates heat:

[0086] Using an infrared sensor to measure the skin surface temperature and a thermistor to measure the ambient temperature, the heat exchanged by radiation can be obtained according to the Slefan-Boltzmann law:

[0087] R=δ·S(T s -T E )

[0088] Where R is the radiation heat dissipation, δ is the radiation coefficient, S is the radiation area, T s is the absolute surface temperature, T E is the absolute temperature of the environment.

[0089] 2. Convection generates heat:

[0090] Under certain conditions, convective heat dissipation is also related to the surface temperature of the skin and the ambient temperature. According to Newton's heat transfer formula, convective heat transfer can be expressed as:

[0091] C=h t (t u -t f )

[0092] Where C is the convective heat transfer; h t is the convective heat transfer coefficient; t u is the body surface temperature; t f is the ambient temperature.

[0093] 3. Evaporation generates heat:

[0094] Humidity sensors are used to measure the relative humidity RHskin near the skin surface and the relative humidity RHenv of the environment;

[0095] According to the Tetens formula, the saturated water vapor pressure P at the corresponding temperature is calculated. sat (T):

[0096]

[0097] According to the partial pressure formula, the water vapor partial pressure P near the skin surface is calculated. skin and the ambient water vapor pressure P env ;

[0098] The evaporation rate is calculated using the following formula

[0099]

[0100] Where A is the skin surface area, h D is the water vapor diffusion coefficient (related to wind speed, air density, etc., L v is the latent heat of vaporization of water (J / kg), which is approximately 2260 J / g or 2.26 MJ / kg.

[0101] Calculate the heat of evaporation using the following formula:

[0102]

[0103] When measuring blood flow velocity, the rate of heat transfer from the body's surface depends not only on the body's surface temperature and the temperature of the metal rod, but is also closely related to blood flow in the capillaries. Faster blood flow removes heat from the body's surface more quickly, affecting the temperature of the metal rod. Typically, blood flow velocity can be inferred by measuring the temperature changes T1 and T2 at both ends of the metal rod.

[0104] Use a thermistor to measure the temperature T1 at the end of the metal rod closest to the body surface and the temperature T2 at the end away from the body surface. Simultaneously measure the body surface temperature Tbody and the surface temperature of the metal rod Tlead (the above four parameters are in degrees Celsius or K). The heat transfer rate is expressed as follows:

[0105] Q=h·A·(T body -T lead )

[0106] Q: Heat transfer rate between the body surface and the heat conductor (unit: J / s)

[0107] h: heat transfer coefficient, the heat transfer capacity between the body surface and the heat conductor (unit: W / m 2 K)

[0108] A: The contact area between the heat conductor and the surface (unit: m 2 )

[0109] T body : Body surface temperature (unit: ℃ or K)

[0110] T lead : Surface temperature of heat conductor (unit: ℃ or K)

[0111]

[0112] T1: The temperature of the end of the heat conductor close to the surface (unit: °C or K)

[0113] T2: The temperature of the end of the heat conductor away from the surface (unit: °C or K)

[0114] L: Length of the thermal conductor (unit: m)

[0115] Combining the above two formulas, we can derive the empirical formula for blood flow velocity:

[0116]

[0117] Through experiments, combined with the empirical coefficient C obtained by calibration, Q and Vb can be related to obtain the relationship between heat transfer rate and blood flow rate.

[0118] When obtaining blood oxygen saturation, theoretically, blood oxygen saturation (SpO2) is the ratio of oxygenated hemoglobin (HbO2) to total hemoglobin in the blood. Its optical measurement device is realized through the principle of pulse oximetry. The measurement formula is as follows:

[0119] SpO2=110-25×R

[0120] Where R = A 660 / A 880 , A 660 and A 880 represent the absorbance under red light and near-infrared light, respectively.

[0121] The required measuring parts are:

[0122] Light source: Red LED and near-infrared LED emit light of different wavelengths (usually 660nm and 880nm respectively);

[0123] Used to receive the intensity of transmitted light after passing through the tissue, usually placed on the other side opposite to the light source;

[0124] The absorbance at two wavelengths is calculated, and then the blood oxygen saturation is calculated.

[0125] In some embodiments, the infrared spectrum detection device includes:

[0126] An optical path module, comprising a near-infrared light source, a photodetector, an optical fiber adapter, and an optical fiber collimator;

[0127] Regional temperature control module;

[0128] Regional pressure detection module.

[0129] like Figure 8 As shown, the infrared spectrum detection module includes an optical path module, a regional temperature control module, and a regional pressure detection module. The optical path module includes a near-infrared light source, a photodetector, a fiber optic adapter, and a fiber optic collimator. When the temperature and pressure are adjusted appropriately, for example, the temperature change is basically stabilized within the range of 36.5±0.5℃, and the optimal pressure is 20N / cm 2, detection begins. The built-in near-infrared light source illuminates, and the photoelectric sensor receives the near-infrared diffuse reflection signal from the fingertips. Changes in blood glucose concentration manifest as changes in glucose concentration in the dermis, and water-soluble living components like glucose are virtually absent in the subcutaneous tissue layer. The diffuse reflection spectrum information received by the photoelectric detector consists of a variable signal caused by changes in component concentrations in the finger tissue and an invariant signal due to the tissue's inherent absorption. By analyzing the spectral contribution of glucose in the diffuse reflection light and combining it with the known correlation between glucose and blood glucose, the blood glucose concentration is calculated.

[0130] In addition to the above-mentioned physiological parameter acquisition device, the present invention also provides a physiological parameter acquisition method based on the device, such as Figure 9 As shown, the method includes the following steps:

[0131] S610: Collecting the pulse signal, metabolic data and near-infrared diffuse reflection signal of the subject; wherein collecting the metabolic data of the subject specifically includes collecting the body temperature data, body surface humidity data, blood flow rate data and blood oxygen saturation data of the subject.

[0132] S620: generating a blood glucose concentration value according to the near-infrared diffuse reflectance signal;

[0133] S630: Generate a visualized physiological parameter collection result from the pulse signal, the metabolic data, and the blood glucose concentration value.

[0134] In some embodiments, collecting metabolic data of the subject further includes:

[0135] The temperature, humidity, blood flow rate and blood oxygen saturation information related to metabolic heat are converted into data, and ultimately reflect the blood glucose concentration.

[0136] In some embodiments, generating a blood glucose concentration value according to the near-infrared diffuse reflectance signal specifically includes:

[0137] By analyzing the spectral contribution of glucose in the diffuse reflected light and combining the known correlation between glucose and blood sugar, the blood sugar concentration value is calculated.

[0138] In the above-mentioned specific embodiment, the physiological parameter acquisition device provided by the present invention includes a host, a wristband 2, a pulse signal acquisition device, a metabolic heat detection component, an infrared spectrum detection device and a control device; wherein, the wristband 2 is used to be mounted on the wrist 100 of the person to be tested, and the pulse signal acquisition device is installed on the wristband 2 and obtains the pulse signal of the person to be tested; the metabolic heat detection device is installed on the host and collects the metabolic data of the person to be tested, and the infrared spectrum detection device is installed on the host and collects the near-infrared diffuse reflection signal of the target part of the person to be tested; the control device is used to receive the pulse signal, the metabolic data and the near-infrared diffuse reflection signal, and generate a blood glucose concentration value based on the near-infrared diffuse reflection signal; the control device is also used to generate a visualized physiological parameter acquisition result from the pulse signal, the metabolic data and the blood glucose concentration value.

[0139] Thus, the physiological parameter acquisition device provided by the present invention integrates a pulse signal acquisition device, a metabolic heat detection device, and an infrared spectrum detection device into a wristband 2, thereby enabling the acquisition of pulse signals, metabolic data, and near-infrared diffuse reflectance signals, and further enabling the generation of visualizations of pulse, metabolic data, and blood glucose concentration values. This solves the problems of existing physiological parameter health monitors, which suffer from single functions, invasive blood glucose measurement, and inconvenient operation. By achieving integrated physiological parameter acquisition, the device avoids the operational inconveniences associated with invasive measurement.

[0140] Furthermore, this multi-parameter health monitor, by utilizing a composite high-precision infrared sensor and metabolic heat integration technology, combined with traditional Chinese medicine pulse diagnosis and non-invasive Western medicine technology, provides users with a brand-new health monitoring experience. This product has demonstrated significant beneficial effects, mainly reflected in the following aspects:

[0141] Firstly, by utilizing a composite, high-precision infrared sensor and metabolic thermal integration technology, this product can accurately measure and display multiple key physiological parameters, including blood glucose, blood oxygen, and peripheral pulse, in real time. This comprehensive monitoring capability enables users to gain a comprehensive understanding of their health status, providing strong support for disease prevention, detection, and management.

[0142] Secondly, this product combines Traditional Chinese Medicine pulse diagnosis with non-invasive Western medicine technology, enabling painless and convenient health monitoring. Compared to traditional blood sugar measurement methods involving needle pricks, this product's non-invasive technology significantly reduces user pain and discomfort, improving measurement comfort and acceptance. Furthermore, Traditional Chinese Medicine pulse diagnosis, coupled with an automated pressurized airbag, provides more comprehensive and accurate monitoring results, providing users with more reliable health data.

[0143] In addition, this product features a real-time feedback transmission mechanism that synchronizes monitoring data to a mobile app, enabling real-time monitoring of physiological health. Users can access their health data anytime, anywhere via their phone, promptly identify abnormalities, and take appropriate intervention and management measures. This convenience not only enhances users' health awareness but also provides a more efficient and convenient means of disease prevention and management.

[0144] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention, rather than to limit it. Although the present invention has been described in detail with reference to the aforementioned embodiments, those skilled in the art should understand that they can still modify the technical solutions described in the aforementioned embodiments, or make equivalent replacements for some of the technical features therein. However, these modifications or replacements do not deviate the essence of the corresponding technical solutions from the spirit and scope of the technical solutions of the various embodiments of the present invention.

Claims

1. A physiological parameter acquisition device, characterized in that: include: A host, the host comprising a housing having a plurality of finger grooves formed therein, an air pump mounted within the housing, a metabolic heat detection assembly for collecting metabolic data of a subject, and an infrared spectrum detection device for collecting near-infrared diffuse reflectance signals from a target area of ​​the subject, the metabolic heat detection assembly and the infrared spectrum detection device being disposed within the finger grooves; A wristband (2), the wristband (2) being used to be placed on the wrist (100) of a person to be tested; A pulse signal acquisition device, which is installed on the wristband (2) and acquires the pulse signal of the person to be measured; The pulse signal acquisition device comprises: An airbag assembly, the airbag assembly being installed in the wristband (2) and being in communication with the air pump; a pulse pressure sensor (22), the pulse pressure sensor (22) being used to collect a current pressure value of the airbag assembly; an air pump, connected to the airbag assembly and configured to inflate the airbag assembly; Both the host and the wristband are provided with an air pump interface, which is connected to the air pump interface on the host through a pneumatic pipe. Both the host and the wristband are provided with a data cable interface, which is connected to the data cable interface on the host through a data cable.

2. The physiological parameter acquisition device according to claim 1, characterized in that: The pneumatic pipeline is a hose.

3. The physiological parameter acquisition device according to claim 1, characterized in that: The airbag assembly comprises at least two airbags (21), and each of the airbags (21) is stacked and arranged along the radial direction of the wristband (2).

4. The physiological parameter acquisition device according to claim 1, characterized in that: The airbag components are in at least three groups, and each of the airbag components is arranged along the tangential direction of the wristband (2).

5. The physiological parameter acquisition device according to claim 1, characterized in that: The metabolic heat detection component includes a temperature sensor, an infrared sensor, a humidity sensor and an optical measuring device.

6. The physiological parameter acquisition device according to claim 1, characterized in that: There are four finger grooves.

7. The physiological parameter acquisition device according to claim 1, characterized in that: The main body shell is provided with a charging port, a power button and a display screen.

8. The physiological parameter acquisition device according to claim 1, characterized in that: The shell is made of TPU material.

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