Portable oxygen generator with blood oxygen saturation detection function and control system thereof

Abstract

The present application relates to oxygen generator technical field, specifically to a portable oxygen generator with blood oxygen saturation detection function and a control system thereof. The present application obtains the low oxygen moment and the apnea compensation coefficient of each low oxygen moment by the data distribution of different moments in different curves. The motion compensation coefficient of the latest low oxygen moment is obtained according to the local respiratory flow rate distribution of the latest low oxygen moment on the respiratory flow rate signal curve and the local heart rate distribution of the latest low oxygen moment on the heart rate signal curve. The sympathetic nerve weight of the latest low oxygen moment is obtained according to the change of heart rate on the heart rate signal curve before different low oxygen moments and the data distribution of different moments on the blood oxygen saturation signal curve in the neighborhood range. The blood oxygen saturation of real time moment is adjusted. The present application obtains accurate blood oxygen saturation by analyzing the coupling of respiration, heart rate and blood oxygen, and improves the accuracy of oxygen production control.

Description

Technical Field

[0001] This invention relates to the field of oxygen concentrator technology, specifically to a portable oxygen concentrator with blood oxygen saturation detection function and its control system. Background Technology

[0002] An intelligent oxygen generation system integrating embedded blood oxygen detection, adaptive oxygen supply adjustment, and low-power portable design improves the dynamic response capability to the user's real-time physiological state. Portable oxygen concentrators rely on blood oxygen saturation detection results to dynamically adjust oxygen supply output; therefore, it is necessary to analyze the blood oxygen saturation detection results.

[0003] In existing technologies, adaptive algorithms, such as LSTM neural networks, are used to process blood oxygen saturation detection results to predict blood oxygen change trends and adjust oxygen supply output. However, blood oxygen detection equipment is subject to interference from various environmental factors in practical applications. Especially in scenarios such as high altitude and high exercise intensity, blood oxygen data may show a false decrease, causing the original adaptive control system to be unable to adjust oxygen supply in a timely manner. Summary of the Invention

[0004] To address the issue of falsely low blood oxygen saturation data, which prevents existing adaptive control systems from adjusting oxygen supply in a timely manner, this invention aims to provide a portable oxygen concentrator and its control system with blood oxygen saturation detection functionality. The specific technical solution adopted is as follows:

[0005] A portable oxygen concentrator with blood oxygen saturation detection function includes an oxygen concentrator body and an oxygen concentrator control system. The oxygen concentrator control system includes a controller and a blood oxygen saturation detector, a respiration detector, and a heart rate detector connected to the controller via signals. The blood oxygen saturation detector is used to detect a blood oxygen saturation signal curve, the respiration detector is used to detect a respiratory flow rate signal curve, and the heart rate detector is used to detect a heart rate signal curve. The controller performs the following steps:

[0006] Blood oxygen saturation signal curves, respiratory flow rate signal curves, and heart rate signal curves were acquired sequentially.

[0007] Based on the data distribution at different times in different curves, the hypoxic time and the apnea compensation coefficient at each hypoxic time were obtained.

[0008] The exercise compensation coefficient at the latest hypoxia time is obtained based on the local respiratory flow rate distribution on the respiratory flow rate signal curve and the local heart rate distribution on the heart rate signal curve at the latest hypoxia time.

[0009] Based on the changes in heart rate on the heart rate signal curve before different hypoxic moments, and the data distribution of blood oxygen saturation signal curve at different moments in the neighborhood, the sympathetic nerve weights at the latest hypoxic moment are obtained.

[0010] Based on the apnea compensation coefficient, exercise compensation coefficient, and sympathetic nerve weight corresponding to the latest hypoxic moment, the real-time blood oxygen saturation is adjusted to obtain the real-time corrected blood oxygen saturation, and the oxygen concentrator is controlled.

[0011] Furthermore, the method for obtaining the hypoxic moment includes:

[0012] If there is a moment on the blood oxygen saturation signal curve where the blood oxygen saturation is lower than the preset blood oxygen saturation baseline, the corresponding moment will be regarded as a moment of hypoxia.

[0013] Furthermore, the method for obtaining the apnea compensation coefficient includes:

[0014] Based on the respiratory flow rate distribution at different times in the respiratory flow rate signal curve, multiple apnea time periods are obtained;

[0015] If any hypoxic moment falls within a breathing apnea period, obtain the difference between the mean heart rate on the heart rate signal curve at all moments during the breathing apnea period and the preset heart rate baseline, calculate the ratio of the difference result to the preset heart rate baseline, and use it as the percentage increase in heart rate.

[0016] The apnea compensation coefficient for the corresponding hypoxic time was obtained based on the duration of the apnea period, the percentage increase in heart rate, and the fluctuation of respiratory flow rate at different times. The duration and percentage increase in heart rate were positively correlated with the apnea compensation coefficient, while the fluctuation of respiratory flow rate was negatively correlated with the apnea compensation coefficient.

[0017] If any hypoxic moment does not fall within a period of respiratory arrest, the apnea compensation coefficient for the corresponding hypoxic moment is set to 0.

[0018] Furthermore, the method for obtaining the apnea time period includes:

[0019] For any given time, the mean of the first derivative of the respiratory flow rate signal curve at different times within the neighborhood is obtained as the respiratory flow rate fluctuation amplitude; the mean of the respiratory flow rate at all times within the neighborhood is obtained as the average respiratory flow rate.

[0020] If the fluctuation range of respiratory flow rate is less than the preset range threshold, and the average respiratory flow rate is less than the preset flow threshold, the corresponding moment will be taken as the moment of apnea.

[0021] If the duration of consecutive apnea moments exceeds a preset duration threshold, the consecutive apnea moments will be considered as an apnea period.

[0022] Furthermore, the method for obtaining the motion compensation coefficient includes:

[0023] Within the time range prior to the latest hypoxic moment, the difference in respiratory flow rate between each moment and the previous moment is obtained, and the difference between the previous moments is obtained, thus obtaining the rate of change of respiratory flow rate between each moment and the previous moment.

[0024] If there is a preset rate of change of continuous respiratory flow rate greater than a preset rate of change threshold, the blood volume change factor at the latest time of hypoxia is obtained based on the local heart rate distribution on the heart rate signal curve at the latest time of hypoxia.

[0025] If the blood volume change factor is less than the preset factor threshold, the exercise compensation coefficient is obtained based on the rate of change of respiratory flow rate and the blood volume change factor between the latest hypoxia time and the previous time. The rate of change of respiratory flow rate is positively correlated with the exercise compensation coefficient, and the blood volume change factor is negatively correlated with the exercise compensation coefficient.

[0026] Conversely, the exercise compensation coefficient for the latest hypoxic moment was set to 0.

[0027] Furthermore, the method for obtaining the blood volume change factor includes:

[0028] The range of heart rate within a local area at the latest hypoxic moment in the heart rate signal curve, and the ratio of the mean heart rate, are obtained as factors affecting blood volume changes.

[0029] Furthermore, the method for obtaining the sympathetic nerve weights includes:

[0030] Obtain the RR intervals of multiple cardiac cycles on the heart rate signal curve prior to each hypoxic moment;

[0031] Based on the fluctuation of a preset number of RR intervals corresponding to each hypoxic moment, heart rate variability, and the difference in blood oxygen saturation between adjacent moments within the neighborhood, the sympathetic nerve weights for each hypoxic moment are obtained. The fluctuation, heart rate variability, and the difference in blood oxygen saturation are all positively correlated with the sympathetic nerve weights.

[0032] Furthermore, the method for obtaining the blood oxygen corrected saturation includes:

[0033] The coupling weights for the latest hypoxic moment are obtained based on the apnea compensation coefficient, exercise compensation coefficient, and sympathetic nerve weights corresponding to the latest hypoxic moment.

[0034] Based on the coupling weights at the latest hypoxic moment, the real-time detected blood oxygen saturation, and the difference between the real-time detected blood oxygen saturation and the preset blood oxygen saturation baseline, the real-time corrected blood oxygen saturation is obtained. The coupling weights, the real-time detected blood oxygen saturation, and the difference between the real-time detected blood oxygen saturation and the preset blood oxygen saturation baseline are all positively correlated with the corrected blood oxygen saturation.

[0035] Furthermore, the method for obtaining the coupling weights includes:

[0036] Obtain the product of the apnea compensation coefficient and the exercise compensation coefficient corresponding to the latest hypoxic moment, and obtain the Euclidean norm of the apnea compensation coefficient and the exercise compensation coefficient corresponding to the latest hypoxic moment; based on the product result, the Euclidean norm, and the sympathetic nerve weight, obtain the coupling weight of the latest hypoxic moment; the product result is positively correlated with the coupling weight, and both the Euclidean norm and the sympathetic nerve weight are negatively correlated with the coupling weight.

[0037] This invention also proposes a portable oxygen concentrator control system with blood oxygen saturation detection function, including a controller and a blood oxygen saturation detector, a respiration detector, and a heart rate detector connected to the controller via signals. The controller performs the following steps:

[0038] Blood oxygen saturation signal curves, respiratory flow rate signal curves, and heart rate signal curves were acquired sequentially.

[0039] Based on the data distribution at different times in different curves, the hypoxic time and the apnea compensation coefficient at each hypoxic time were obtained.

[0040] The exercise compensation coefficient at the latest hypoxia time is obtained based on the local respiratory flow rate distribution on the respiratory flow rate signal curve and the local heart rate distribution on the heart rate signal curve at the latest hypoxia time.

[0041] Based on the changes in heart rate on the heart rate signal curve before different hypoxic moments, and the data distribution of blood oxygen saturation signal curve at different moments in the neighborhood, the sympathetic nerve weights at the latest hypoxic moment are obtained.

[0042] Based on the apnea compensation coefficient, exercise compensation coefficient, and sympathetic nerve weight corresponding to the latest hypoxic moment, the real-time blood oxygen saturation is adjusted to obtain the real-time corrected blood oxygen saturation, and the oxygen concentrator is controlled.

[0043] The present invention has the following beneficial effects:

[0044] This invention obtains the hypoxic moment and the apnea compensation coefficient for each hypoxic moment based on the data distribution at different times in different curves, accurately identifying hypoxic events and quantifying the compensatory capacity of the respiratory system. Based on the local respiratory flow rate distribution on the respiratory flow signal curve and the local heart rate distribution on the heart rate signal curve at the latest hypoxic moment, it obtains the exercise compensation coefficient for the latest hypoxic moment, reflecting the comprehensive compensatory adjustments made by the respiratory and circulatory systems to cope with hypoxic environments during exercise. Based on the changes in heart rate on the heart rate signal curve before different hypoxic moments and the data distribution on the blood oxygen saturation signal curve at different times within the neighborhood, it obtains the sympathetic nerve weight at the latest hypoxic moment, which helps to deepen the understanding of the body's neural regulatory mechanisms under hypoxic conditions. Based on the apnea compensation coefficient, exercise compensation coefficient, and sympathetic nerve weight corresponding to the latest hypoxic moment, it adjusts the real-time detected blood oxygen saturation to obtain real-time corrected blood oxygen saturation, improving the accuracy of blood oxygen monitoring and controlling the oxygen concentrator. This invention obtains accurate blood oxygen saturation by analyzing the coupling of respiration, heart rate, and blood oxygen, thereby improving the precision of oxygen production control. Attached Figure Description

[0045] To more clearly illustrate the technical solutions and advantages in the embodiments of the present invention or the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments of the present invention. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0046] Figure 1 This is a control flowchart of a portable oxygen concentrator with blood oxygen saturation detection function provided in one embodiment of the present invention;

[0047] Figure 2 A flowchart illustrating a method for obtaining the apnea compensation coefficient according to an embodiment of the present invention;

[0048] Figure 3 This is a flowchart illustrating a method for obtaining motion compensation coefficients according to an embodiment of the present invention. Detailed Implementation

[0049] To further illustrate the technical means and effects adopted by the present invention to achieve its intended purpose, the following, in conjunction with the accompanying drawings and preferred embodiments, details the specific implementation, structure, features, and effects of a portable oxygen concentrator and its control system with blood oxygen saturation detection function according to the present invention. In the following description, different "one embodiment" or "another embodiment" do not necessarily refer to the same embodiment. Furthermore, specific features, structures, or characteristics in one or more embodiments can be combined in any suitable form.

[0050] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this invention pertains.

[0051] The following description, in conjunction with the accompanying drawings, details a specific solution for a portable oxygen concentrator with blood oxygen saturation detection function and its control system provided by the present invention.

[0052] This invention proposes a portable oxygen concentrator with blood oxygen saturation detection function, including an oxygen concentrator body comprising a compressor, a molecular sieve, a solenoid valve, an oxygen concentration sensor, and a blood oxygen concentration detection module. This portable oxygen concentrator integrates blood oxygen saturation detection functionality, separating oxygen from the air using molecular sieve pressure swing adsorption technology. Through real-time monitoring, adaptive control, and multi-sensor fusion, it achieves a shift from "passive oxygen supply" to "active intervention." The invention also includes an oxygen concentrator control system, comprising a controller and a blood oxygen saturation detector, a respiration detector, and a heart rate detector connected to the controller. The blood oxygen saturation detector detects the blood oxygen saturation signal curve, the respiration detector detects the respiratory flow rate signal curve, and the heart rate detector detects the heart rate signal curve. The controller implements the following steps: [See details]. Figure 1 It illustrates a control flowchart of a portable oxygen concentrator with blood oxygen saturation detection function according to an embodiment of the present invention, specifically including:

[0053] Step S1: Obtain the blood oxygen saturation signal curve, respiratory flow signal curve, and heart rate signal curve in sequence.

[0054] In the embodiments of the present invention, considering that in reality, the slow wave period disorder of the SpO2 signal may be related to respiratory drive or abnormal cardiovascular function, and the problem of false decline may also occur, it is necessary to conduct a holistic analysis in conjunction with the changes in respiratory and heart rate; firstly, the blood oxygen saturation detection adopts a finger clip photoelectric blood oxygen sensor, which is compatible with SpO2 detection technology and supports wired and wireless blood oxygen detection. The detected data can be transmitted through USB-C or other customized wired connection interfaces; it also supports multiple wireless data transmissions such as Bluetooth and Wi-Fi. The time-series blood oxygen saturation SpO2 curve is obtained through the blood oxygen saturation detector, and the user's respiratory flow signal curve and heart rate signal curve are obtained through a wearable device containing a respiratory flow detector and a heart rate detector, wherein the timestamps of the acquired signals are aligned.

[0055] It should be noted that time-domain normalization was performed on all signals to eliminate interference from talking, coughing, etc. in the respiratory flow signal, as well as artifacts in the heart rate signal.

[0056] Step S2: Based on the data distribution at different times in different curves, obtain the hypoxic time and the apnea compensation coefficient at each hypoxic time.

[0057] The amplitude of the blood oxygen saturation signal curve reflects the difference in blood's absorption of light. During respiratory arrest or heart rate fluctuations, blood oxygen saturation may show a false decrease due to hemodynamic changes. Therefore, by analyzing the data distribution at different times within different curves, the hypoxic moments are confirmed; and the apnea compensation coefficient is quantified to reflect the body's physiological compensatory capacity for hypoxia. Based on the data distribution at different times within different curves, the hypoxic moments and the apnea compensation coefficient for each hypoxic moment are obtained.

[0058] Preferably, in one embodiment of the present invention, the method for obtaining the hypoxic moment includes:

[0059] If there is a moment on the blood oxygen saturation signal curve where the blood oxygen saturation is lower than the preset blood oxygen saturation baseline, the corresponding moment will be regarded as a moment of hypoxia.

[0060] It should be noted that, in one embodiment of the present invention, the preset blood oxygen saturation baseline is the blood oxygen saturation measured in a resting state. In other embodiments of the present invention, the preset blood oxygen saturation baseline can be set according to specific circumstances, and will not be limited or elaborated here.

[0061] Preferably, in one embodiment of the present invention, the method for obtaining the apnea compensation coefficient is described in [reference needed]. Figure 2 It shows a flowchart of a method for obtaining the apnea compensation coefficient, including:

[0062] Step S201: Based on the respiratory flow rate distribution at different times in the respiratory flow rate signal curve, obtain multiple apnea time periods.

[0063] It should be noted that, in one embodiment of the present invention, the method for obtaining the apnea time period includes:

[0064] For any given time, the mean of the first derivative of the respiratory flow rate signal curve at different times within the neighborhood is obtained as the respiratory flow rate fluctuation amplitude; the mean of the respiratory flow rate at all times within the neighborhood is obtained as the average respiratory flow rate.

[0065] If the fluctuation range of respiratory flow rate is less than the preset range threshold, and the average respiratory flow rate is less than the preset flow rate threshold, the corresponding time will be regarded as the time of apnea.

[0066] If the duration of consecutive apnea moments exceeds a preset duration threshold, the consecutive apnea moments will be considered as an apnea period.

[0067] It should be noted that, in one embodiment of the present invention, the method for obtaining the neighborhood range includes taking each moment as a reference and forming a range of a preset duration with historical moments, wherein the preset duration is 3 seconds. In other embodiments of the present invention, the size of the preset duration can be set according to specific circumstances, and will not be limited or elaborated here.

[0068] It should be noted that, in one embodiment of the present invention, the preset amplitude threshold is set to 0.2, the preset flow rate threshold is set to 0.1, and the preset duration threshold is set to 5 seconds. In other embodiments of the present invention, the values ​​of the preset amplitude threshold, the preset flow rate threshold, and the preset duration threshold can be set according to specific circumstances, and are not limited or elaborated here.

[0069] Step S202: If any hypoxic moment falls within a breathing apnea period, obtain the difference between the mean heart rate on the heart rate signal curve at all moments during the breathing apnea period and the preset heart rate baseline, and calculate the ratio of the difference result to the preset heart rate baseline as the percentage increase in heart rate.

[0070] Sleep apnea causes a drop in blood oxygen. During periods of low oxygen and sleep apnea, the heart rate increases. Therefore, the greater the difference between the mean heart rate during sleep apnea and the preset baseline heart rate, the greater the heart rate during sleep apnea and the greater the percentage increase in heart rate.

[0071] It should be noted that, in order to eliminate short-term fluctuations, in the embodiments of the present invention, the method for obtaining the preset heart rate baseline is to sort the heart rates in ascending order within 5 minutes before the start of the apnea period and obtain the heart rate at the 10th percentile as the preset heart rate baseline; the specific means are well known to those skilled in the art and will not be described in detail here.

[0072] Step S203: Based on the duration of the apnea period, the percentage increase in heart rate, and the degree of fluctuation in respiratory flow rate at different times during the hypoxic period, obtain the apnea compensation coefficient for the corresponding hypoxic period. The duration and percentage increase in heart rate are positively correlated with the apnea compensation coefficient, while the degree of fluctuation in respiratory flow rate is negatively correlated with the apnea compensation coefficient.

[0073] It should be noted that, in one embodiment of the present invention, the degree of fluctuation can be represented by calculating the standard deviation. The larger the standard deviation, the greater the degree of fluctuation, and the smaller the standard deviation, the smaller the degree of fluctuation. In other embodiments of the present invention, the degree of fluctuation can also be reflected by calculating the variance. The specific means are well known to those skilled in the art and will not be described in detail here.

[0074] It should be noted that the longer the duration of the apnea period during a hypoxic event, the more severe the hypoxia, the greater the need for compensation, and the higher the apnea compensation coefficient. The greater the percentage increase in heart rate, the greater the direct compensation for hypoxia, and the higher the apnea compensation coefficient. The greater the fluctuation in respiratory flow rate, the more unstable the respiratory control, the worse the respiratory efficiency, and the lower the apnea compensation coefficient. Therefore, the duration and percentage increase in heart rate are positively correlated with the apnea compensation coefficient, while the fluctuation in respiratory flow rate is negatively correlated with the apnea compensation coefficient.

[0075] In one embodiment of the present invention, the product of the duration of the apnea period during the hypoxic moment and the percentage increase in heart rate is obtained, and the ratio of the product result to the degree of fluctuation is calculated as the apnea compensation coefficient for the corresponding hypoxic moment. Therefore, based on the above basic mathematical operations, a correlation is constructed between the duration of the apnea period during the hypoxic moment, the percentage increase in heart rate, the degree of fluctuation in respiratory flow at different times, and the apnea compensation coefficient. That is, the greater the duration, the greater the percentage increase in heart rate, the more severe the fluctuation, and the greater the apnea compensation coefficient.

[0076] Step S204: If any hypoxic moment does not fall within a breathing apnea period, set the breathing apnea compensation coefficient for the corresponding hypoxic moment to 0.

[0077] Step S3: Based on the local respiratory flow rate distribution on the respiratory flow rate signal curve at the latest hypoxic moment and the local heart rate distribution on the heart rate signal curve at the latest hypoxic moment, obtain the exercise compensation coefficient at the latest hypoxic moment.

[0078] During exercise, the surge in skeletal muscle oxygen consumption triggers local vasodilation. The remodeling of peripheral blood oxygen distribution alters the proportion of blood volume in the microcirculation zone where the SpO2 probe is located. The local distribution characteristics of respiratory flow rate and heart rate signals reflect the adaptive adjustments of the respiratory and circulatory systems to hypoxia. Based on the local respiratory flow rate distribution on the respiratory flow rate signal curve and the local heart rate distribution on the heart rate signal curve at the latest hypoxia moment, the exercise compensation coefficient at the latest hypoxia moment is obtained.

[0079] Preferably, in one embodiment of the present invention, the method for obtaining the motion compensation coefficient is described in [reference needed]. Figure 3 It shows a flowchart of a method for obtaining motion compensation coefficients, including:

[0080] Step S301: For the time range before the latest hypoxic moment, obtain the difference in respiratory flow rate between each moment and the previous moment, and the difference between the previous moments, to obtain the rate of change of respiratory flow rate between each moment and the previous moment.

[0081] The greater the difference in respiratory flow rate between each moment and the previous moment, the greater the instantaneous rate of change of respiratory flow rate, and the greater the respiratory state.

[0082] Step S302: If there is a preset rate of change of continuous respiratory flow rate greater than a preset rate of change threshold, obtain the blood volume change factor at the latest time of hypoxia based on the local heart rate distribution on the heart rate signal curve at the latest time of hypoxia.

[0083] Preferably, in one embodiment of the present invention, the method for obtaining the blood volume change factor includes:

[0084] The range of heart rate within a local area at the latest hypoxic moment in the heart rate signal curve, and the ratio of the mean heart rate, are obtained as factors affecting blood volume changes.

[0085] Step S303: If the blood volume change factor is less than the preset factor threshold, the exercise compensation coefficient is obtained based on the rate of change of respiratory flow rate and the blood volume change factor between the latest hypoxia time and the previous time. The rate of change of respiratory flow rate is positively correlated with the exercise compensation coefficient, and the blood volume change factor is negatively correlated with the exercise compensation coefficient.

[0086] In one embodiment of the present invention, the respiratory flow rate change rate is normalized and mapped based on a sine function to obtain the difference between the positive integer 1 and the blood volume change factor, which is taken as the first difference. The sum of the normalized mapping result and the first difference is calculated as the exercise compensation coefficient at the time of hypoxia. Therefore, based on the above-mentioned basic mathematical operations, the correlation between the respiratory flow rate change rate, the blood volume change factor and the exercise compensation coefficient is constructed. That is, the greater the respiratory flow rate change rate, the smaller the blood volume change factor, the greater the respiratory state, the greater the vasodilation, the more serious the blood oxygen distortion caused by exercise, the greater the need for exercise compensation, and the greater the exercise compensation coefficient.

[0087] Step S304: Conversely, the exercise compensation coefficient for the latest hypoxic moment is set to 0.

[0088] It should be noted that, in one embodiment of the present invention, the time range before the latest hypoxia moment is 20 seconds, the preset number is set to 3, the preset rate of change threshold is set to 1.5, and the preset factor threshold is set to 0.3. In other embodiments of the present invention, the size of the time range before the latest hypoxia moment, the preset number, the preset rate of change threshold, and the preset factor threshold can be specifically set according to the specific situation, and will not be limited or elaborated here.

[0089] Step S4: Based on the changes in heart rate on the heart rate signal curve before different hypoxic moments, and the data distribution of blood oxygen saturation signal curve at different moments in the neighborhood, obtain the sympathetic nerve weights at the latest hypoxic moment.

[0090] Hypoxia triggers sympathetic nerve excitation, leading to increased heart rate and vasoconstriction, which in turn excites the sympathetic nervous system. By analyzing changes in heart rate and the distribution of blood oxygen saturation data, the weight of the sympathetic nervous system can be more comprehensively quantified. Based on changes in heart rate on the heart rate signal curve before different hypoxic moments and the distribution of blood oxygen saturation signal curves at different times within the neighborhood, the sympathetic nerve weight at the latest hypoxic moment is obtained.

[0091] Preferably, in one embodiment of the present invention, the method for obtaining sympathetic nerve weights includes:

[0092] Obtain the RR intervals of multiple cardiac cycles on the heart rate signal curve prior to each hypoxic moment;

[0093] Based on the fluctuation of a preset number of RR intervals corresponding to each hypoxic moment and the difference in blood oxygen saturation between adjacent moments within the neighborhood, the sympathetic nerve weight for each hypoxic moment is obtained. The fluctuation of the RR interval is negatively correlated with the sympathetic nerve weight, while the difference in blood oxygen saturation is positively correlated with the sympathetic nerve weight.

[0094] It should be noted that the degree of fluctuation in the RR interval reflects the regulatory capacity of the sympathetic nervous system. The smaller the fluctuation, the more the sympathetic nervous system is stimulated, and the greater the weight of the sympathetic nervous system. The rate of decrease in blood oxygen reflects the severity of hypoxia. The greater the rate of decrease in blood oxygen, the more excited the sympathetic nervous system, and the greater the weight of the sympathetic nervous system. Therefore, the degree of fluctuation in the RR interval is negatively correlated with the weight of the sympathetic nervous system, while the difference in blood oxygen saturation is positively correlated with the weight of the sympathetic nervous system.

[0095] In one embodiment of the present invention, the fluctuation degree of a preset number of RR intervals is obtained as heart rate variability. The difference between the preset heart rate variability baseline and the heart rate variability is calculated as the degree of decrease in heart rate variability at each hypoxic moment. The mean difference in blood oxygen saturation between adjacent moments in the neighborhood of each hypoxic moment is obtained and mapped by the natural logarithm as the blood oxygen decrease rate. The degree of decrease in heart rate variability at the latest hypoxic moment is normalized based on the range of the decrease in heart rate variability. The product between the normalization result and the blood oxygen decrease rate is calculated as the sympathetic nerve weight. Therefore, based on the above basic mathematical operations, a correlation is formed between the fluctuation degree and the blood oxygen decrease rate and the sympathetic nerve weight. That is, the smaller the fluctuation degree of the RR interval, the smaller the heart rate variability, the smaller the relative heart rate variability baseline, the greater the blood oxygen decrease rate, the more likely it is to trigger more sympathetic nerves, and the greater the sympathetic nerve weight.

[0096] It should be noted that, in one embodiment of the present invention, based on the waveform characteristics of the QRS complex, the position of the R wave peak in each cardiac cycle of the heart rate signal curve is obtained, and the time interval between each two adjacent R waves is calculated as the RR interval, with a preset number of 30. The preset heart rate variability baseline is obtained based on resting state data, as detailed in other embodiments of the present invention. In other embodiments of the present invention, the preset number can be set according to specific circumstances, and is not limited or elaborated here.

[0097] Step S5: Based on the apnea compensation coefficient, exercise compensation coefficient, and sympathetic nerve weight corresponding to the latest hypoxic moment, adjust the real-time detected blood oxygen saturation to obtain real-time corrected blood oxygen saturation, and control the oxygen concentrator.

[0098] Multiple coupling relationships are integrated and constrained to effectively distinguish between true hypoxia and pseudo-artifacts, enabling dynamic correction of SpO2 values. Based on the apnea compensation coefficient, exercise compensation coefficient, and sympathetic nerve weight corresponding to the latest hypoxia moment, the real-time detected blood oxygen saturation is adjusted to obtain real-time corrected blood oxygen saturation.

[0099] Preferably, in one embodiment of the present invention, the method for obtaining blood oxygen corrected saturation includes:

[0100] The coupling weights for the latest hypoxic moment are obtained based on the apnea compensation coefficient, exercise compensation coefficient, and sympathetic nerve weights corresponding to the latest hypoxic moment.

[0101] Preferably, if apnea and exercise occur simultaneously, they may be coupled and inhibited. In one embodiment of the present invention, the method for obtaining the coupling weight includes:

[0102] Obtain the product of the apnea compensation coefficient and the exercise compensation coefficient corresponding to the latest hypoxic moment, and obtain the Euclidean norm of the apnea compensation coefficient and the exercise compensation coefficient corresponding to the latest hypoxic moment.

[0103] The coupling weight at the latest hypoxia time is obtained based on the product result, Euclidean norm, and sympathetic nerve weight. The product result is positively correlated with the coupling weight, while the Euclidean norm and sympathetic nerve weight are both negatively correlated with the coupling weight.

[0104] It should be noted that the larger the product, the larger the apnea compensation coefficient and the exercise compensation coefficient, the greater the impact on hypoxia, and the greater the coupling weight; the larger the Euclidean norm, the greater the distance between the apnea compensation coefficient and the exercise compensation coefficient, the more mutually exclusive they are, and the smaller the coupling weight; the greater the sympathetic nerve weight, the faster the heart rate, the greater the vasoconstriction, the greater the inhibition of other compensations, and the smaller the coupling weight, showing a negative correlation.

[0105] In one embodiment of the present invention, the ratio of the product result at the latest hypoxic moment to the Euclidean norm is obtained as the inconsistency coefficient; the difference between the positive integer 1 and the square of the sympathetic nerve weight is obtained as the compensatory increase coefficient; and the product of the inconsistency coefficient and the compensatory increase coefficient is obtained as the coupling weight. Therefore, through the above basic mathematical operations, the correlation between the product result, the Euclidean norm, the sympathetic nerve weight, and the coupling weight is constructed, that is, the larger the product result, the smaller the Euclidean norm, the smaller the sympathetic nerve weight, and the larger the coupling weight.

[0106] Based on the coupling weights at the latest hypoxic moment, the real-time detected blood oxygen saturation, and the difference between the real-time detected blood oxygen saturation and the preset blood oxygen saturation baseline, the real-time corrected blood oxygen saturation is obtained. The coupling weights, the real-time detected blood oxygen saturation, and the difference between the real-time detected blood oxygen saturation and the preset blood oxygen saturation baseline are all positively correlated with the corrected blood oxygen saturation.

[0107] It should be noted that the larger the coupling weight, the smaller the suppression of compensation, and the greater the blood oxygen correction saturation, showing a positive correlation; the greater the difference between the real-time blood oxygen saturation and the preset blood oxygen saturation baseline, the greater the blood oxygen saturation and the greater the blood oxygen correction saturation, showing a positive correlation.

[0108] In one embodiment of the present invention, the coupling weight k is nonlinearly gain-controlled using the Sigmoid function. The result after control is multiplied by the difference between the real-time detected blood oxygen saturation and the preset blood oxygen saturation baseline. The sum of the multiplication result and the real-time detected blood oxygen saturation is calculated as the real-time corrected blood oxygen saturation. Therefore, the above basic mathematical operations construct the correlation between the coupling weight, the real-time detected blood oxygen saturation, the difference, and the corrected blood oxygen saturation. That is, the larger the coupling weight, the larger the difference, the larger the blood oxygen saturation, and the larger the corrected blood oxygen saturation.

[0109] It should be noted that obtaining real-time blood oxygen saturation correction allows for the control of the oxygen concentrator, including: First, applying the Teager-Kaiser energy operator to the respiratory flow signal processing can detect the inspiration trigger moment, allowing for immediate oxygen supply at that moment instead of waiting for complete signal confirmation; second, utilizing the LSTM model in the data processing unit to capture the evolution of respiratory patterns in the data storage unit and outputting the predicted moment of the next inspiration. The prediction principles of the Teager-Kaiser energy operator and the trained neural network are well-known to technical personnel and will not be elaborated here; third, by using real-time inspiration trigger moments and inspiration prediction moments, the system covers both regular and irregular breathing rhythms of the user, meeting the user's oxygen needs;

[0110] Based on the multimodal dynamic switching of oxygen supply flow rate according to blood oxygen correction saturation, if the blood oxygen correction saturation is greater than or equal to a preset first saturation threshold, it is in steady-state mode, providing continuous low-flow oxygen supply; if the blood oxygen correction saturation is less than a preset second saturation threshold, it is in emergency mode, activating the backup liquid oxygen tank for oxygen supply; if the blood oxygen correction saturation is greater than or equal to the preset second saturation threshold but less than the preset first saturation threshold, it is in compensatory mode, providing gradient pressurized pulse oxygen supply, which helps meet oxygen inhalation needs. The preset first saturation threshold is greater than the preset second saturation threshold, with the preset first saturation threshold being 94% and the preset second saturation threshold being 88%. In other embodiments of this invention, the saturation thresholds can be specifically set according to specific circumstances, and are not limited or elaborated here.

[0111] In summary, this invention obtains the hypoxic moment and the apnea compensation coefficient for each hypoxic moment based on the data distribution at different times in different curves; it obtains the exercise compensation coefficient for the latest hypoxic moment based on the local respiratory flow distribution on the respiratory flow signal curve and the local heart rate distribution on the heart rate signal curve at the latest hypoxic moment; it obtains the sympathetic weight for the latest hypoxic moment based on the heart rate changes on the heart rate signal curve before different hypoxic moments and the data distribution on the blood oxygen saturation signal curve at different times within the neighborhood; and it adjusts the real-time detected blood oxygen saturation to obtain real-time corrected blood oxygen saturation. This invention obtains accurate blood oxygen saturation by analyzing the coupling of respiration, heart rate, and blood oxygen, thus improving the accuracy of oxygen production control.

[0112] This invention also proposes a portable oxygen concentrator control system with blood oxygen saturation detection function. The system includes a controller and a blood oxygen saturation detector, a respiration detector, and a heart rate detector connected to the controller via signals. The controller performs the following steps:

[0113] Blood oxygen saturation signal curves, respiratory flow rate signal curves, and heart rate signal curves were acquired sequentially.

[0114] Based on the data distribution at different times in different curves, the hypoxic time and the apnea compensation coefficient at each hypoxic time were obtained.

[0115] The exercise compensation coefficient at the latest hypoxia time is obtained based on the local respiratory flow rate distribution on the respiratory flow rate signal curve and the local heart rate distribution on the heart rate signal curve at the latest hypoxia time.

[0116] Based on the changes in heart rate on the heart rate signal curve before different hypoxic moments, and the data distribution of blood oxygen saturation signal curve at different moments in the neighborhood, the sympathetic nerve weights at the latest hypoxic moment are obtained.

[0117] Based on the apnea compensation coefficient, exercise compensation coefficient, and sympathetic nerve weight corresponding to the latest hypoxic moment, the real-time blood oxygen saturation is adjusted to obtain the real-time corrected blood oxygen saturation, and the oxygen concentrator is controlled.

[0118] It should be understood that the portable oxygen concentrator control system with blood oxygen saturation detection function provided in this embodiment is applied to a portable oxygen concentrator with blood oxygen saturation detection function as described above, and therefore has the same steps and beneficial effects as the control system adopted, run or implemented by its stored application.

[0119] It should be noted that the order of the above embodiments of the present invention is merely for descriptive purposes and does not represent the superiority or inferiority of the embodiments. The processes depicted in the accompanying drawings do not necessarily require a specific or sequential order to achieve the desired result. In some embodiments, multitasking and parallel processing are also possible or may be advantageous.

[0120] The various embodiments in this specification are described in a progressive manner. The same or similar parts between the various embodiments can be referred to each other. Each embodiment focuses on describing the differences from other embodiments.

Claims

1. A portable oxygen concentrator with blood oxygen saturation detection function, comprising an oxygen concentrator body, characterized in that, It also includes an oxygen concentrator control system, which includes a controller and a blood oxygen saturation detector, a respiration detector, and a heart rate detector connected to the controller via signals. The blood oxygen saturation detector is used to detect the blood oxygen saturation signal curve, the respiration detector is used to detect the respiratory flow rate signal curve, and the heart rate detector is used to detect the heart rate signal curve. The controller performs the following steps: Blood oxygen saturation signal curves, respiratory flow rate signal curves, and heart rate signal curves were acquired sequentially. Based on the data distribution at different times in different curves, the hypoxic time and the apnea compensation coefficient at each hypoxic time were obtained. The exercise compensation coefficient at the latest hypoxia time is obtained based on the local respiratory flow rate distribution on the respiratory flow rate signal curve and the local heart rate distribution on the heart rate signal curve at the latest hypoxia time. Based on the changes in heart rate on the heart rate signal curve before different hypoxic moments, and the data distribution of blood oxygen saturation signal curve at different moments in the neighborhood, the sympathetic nerve weights at the latest hypoxic moment are obtained. Based on the apnea compensation coefficient, exercise compensation coefficient, and sympathetic nerve weight corresponding to the latest hypoxic moment, the real-time blood oxygen saturation is adjusted to obtain the real-time corrected blood oxygen saturation, and the oxygen concentrator is controlled.

2. A portable oxygen concentrator with blood oxygen saturation detection function according to claim 1, characterized in that, The method for obtaining the hypoxic moment includes: If there is a moment on the blood oxygen saturation signal curve where the blood oxygen saturation is lower than the preset blood oxygen saturation baseline, the corresponding moment will be regarded as a moment of hypoxia.

3. A portable oxygen concentrator with blood oxygen saturation detection function according to claim 1, characterized in that, The method for obtaining the apnea compensation coefficient includes: Based on the respiratory flow rate distribution at different times in the respiratory flow rate signal curve, multiple apnea time periods are obtained; If any hypoxic moment falls within a breathing apnea period, obtain the difference between the mean heart rate on the heart rate signal curve at all moments during the breathing apnea period and the preset heart rate baseline, calculate the ratio of the difference result to the preset heart rate baseline, and use it as the percentage increase in heart rate. The apnea compensation coefficient for the corresponding hypoxic time was obtained based on the duration of the apnea period, the percentage increase in heart rate, and the fluctuation of respiratory flow rate at different times. The duration and percentage increase in heart rate were positively correlated with the apnea compensation coefficient, while the fluctuation of respiratory flow rate was negatively correlated with the apnea compensation coefficient. If any hypoxic moment does not fall within a period of respiratory arrest, the apnea compensation coefficient for the corresponding hypoxic moment is set to 0.

4. A portable oxygen concentrator with blood oxygen saturation detection function according to claim 3, characterized in that, The method for obtaining the apnea time period includes: For any given time, the mean of the first derivative of the respiratory flow rate signal curve at different times within the neighborhood is obtained as the respiratory flow rate fluctuation amplitude; the mean of the respiratory flow rate at all times within the neighborhood is obtained as the average respiratory flow rate. If the fluctuation range of respiratory flow rate is less than the preset range threshold, and the average respiratory flow rate is less than the preset flow threshold, the corresponding moment will be taken as the moment of apnea. If the duration of consecutive apnea moments exceeds a preset duration threshold, the consecutive apnea moments will be considered as an apnea period.

5. A portable oxygen concentrator with blood oxygen saturation detection function according to claim 1, characterized in that, The method for obtaining the motion compensation coefficient includes: Within the time range prior to the latest hypoxic moment, the difference in respiratory flow rate between each moment and the previous moment is obtained, and the difference between the previous moments is obtained, thus obtaining the rate of change of respiratory flow rate between each moment and the previous moment. If there is a preset rate of change of continuous respiratory flow rate greater than a preset rate of change threshold, the blood volume change factor at the latest time of hypoxia is obtained based on the local heart rate distribution on the heart rate signal curve at the latest time of hypoxia. If the blood volume change factor is less than the preset factor threshold, the exercise compensation coefficient is obtained based on the rate of change of respiratory flow rate and the blood volume change factor between the latest hypoxia time and the previous time. The rate of change of respiratory flow rate is positively correlated with the exercise compensation coefficient, and the blood volume change factor is negatively correlated with the exercise compensation coefficient. Conversely, the exercise compensation coefficient for the latest hypoxic moment was set to 0.

6. A portable oxygen concentrator with blood oxygen saturation detection function according to claim 5, characterized in that, The method for obtaining the blood volume change factor includes: The range of heart rate within a local area at the latest hypoxic moment in the heart rate signal curve, and the ratio of the mean heart rate, are obtained as factors affecting blood volume changes.

7. A portable oxygen concentrator with blood oxygen saturation detection function according to claim 1, characterized in that, The method for obtaining the sympathetic nerve weights includes: Obtain the RR intervals of multiple cardiac cycles on the heart rate signal curve prior to each hypoxic moment; Based on the fluctuation of a preset number of RR intervals corresponding to each hypoxic moment and the difference in blood oxygen saturation between adjacent moments within the neighborhood, the sympathetic nerve weights for each hypoxic moment are obtained. The fluctuation of the RR intervals is negatively correlated with the sympathetic nerve weights, while the difference in blood oxygen saturation is positively correlated with the sympathetic nerve weights.

8. A portable oxygen concentrator with blood oxygen saturation detection function according to claim 1, characterized in that, The method for obtaining the blood oxygen corrected saturation includes: The coupling weights for the latest hypoxic moment are obtained based on the apnea compensation coefficient, exercise compensation coefficient, and sympathetic nerve weights corresponding to the latest hypoxic moment. Based on the coupling weights at the latest hypoxic moment, the real-time detected blood oxygen saturation, and the difference between the real-time detected blood oxygen saturation and the preset blood oxygen saturation baseline, the real-time corrected blood oxygen saturation is obtained. The coupling weights, the real-time detected blood oxygen saturation, and the difference between the real-time detected blood oxygen saturation and the preset blood oxygen saturation baseline are all positively correlated with the corrected blood oxygen saturation.

9. A portable oxygen concentrator with blood oxygen saturation detection function according to claim 8, characterized in that, The method for obtaining the coupling weight includes: Obtain the product of the apnea compensation coefficient and the exercise compensation coefficient corresponding to the latest hypoxic moment, and obtain the Euclidean norm of the apnea compensation coefficient and the exercise compensation coefficient corresponding to the latest hypoxic moment. The coupling weight at the latest hypoxia time is obtained based on the product result, Euclidean norm, and sympathetic nerve weight. The product result is positively correlated with the coupling weight, while the Euclidean norm and sympathetic nerve weight are both negatively correlated with the coupling weight.

10. A control system for a portable oxygen concentrator with blood oxygen saturation detection function, characterized in that, The system includes a controller and a blood oxygen saturation detector, a respiration detector, and a heart rate detector that are signal-connected to the controller. The controller performs the following steps: Blood oxygen saturation signal curves, respiratory flow rate signal curves, and heart rate signal curves were acquired sequentially. Based on the data distribution at different times in different curves, the hypoxic time and the apnea compensation coefficient at each hypoxic time were obtained. The exercise compensation coefficient at the latest hypoxia time is obtained based on the local respiratory flow rate distribution on the respiratory flow rate signal curve and the local heart rate distribution on the heart rate signal curve at the latest hypoxia time. Based on the changes in heart rate on the heart rate signal curve before different hypoxic moments, and the data distribution of blood oxygen saturation signal curve at different moments in the neighborhood, the sympathetic nerve weights at the latest hypoxic moment are obtained. Based on the apnea compensation coefficient, exercise compensation coefficient, and sympathetic nerve weight corresponding to the latest hypoxic moment, the real-time blood oxygen saturation is adjusted to obtain the real-time corrected blood oxygen saturation, and the oxygen concentrator is controlled.

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