Method and device for controlling the pressure relief speed of a sphygmomanometer, sphygmomanometer and program product

Abstract

The present application relates to electronic sphygmomanometer technical field, disclose a kind of sphygmomanometer pressure relief speed control method, device, sphygmomanometer and program product. Among them, the method includes: obtaining the pressure signal of sphygmomanometer;Determine the pressure relief speed of sphygmomanometer based on the change of pressure signal;Determine the pressure relief stage matched with the pressure relief speed based on the change of pressure relief speed;According to the control strategy corresponding to pressure relief stage, the opening of the electric control valve of sphygmomanometer is adjusted, and the pressure relief speed is controlled based on the opening result. By implementing the technical scheme of the present application, the pressure relief speed of sphygmomanometer can be accurately controlled to improve the measurement accuracy.

Description

Technical Field

[0001] This invention relates to the field of electronic blood pressure monitor technology, specifically to a method, device, blood pressure monitor, and program product for controlling the pressure release rate of a blood pressure monitor. Background Technology

[0002] Currently, most electronic blood pressure monitors still use fixed mechanical pressure relief valves to achieve slow pressure release. However, the pressure relief characteristics of mechanical valves have limitations, and the pressure release rate may vary in different usage scenarios. In contrast, electronically controlled valves offer greater control freedom and adaptability, allowing for more precise adjustment of the pressure release rate. However, the performance of electronically controlled valves relies on precise control algorithms, and the stability of these algorithms faces the challenge of pulse wave interference. Pulse waves are superimposed on the cuff pressure signal, causing instability in the rate of pressure change, which in turn affects the accuracy of pressure calculation. To reduce this interference, the raw pressure data needs to be filtered. However, due to the nonlinearity and time-varying nature of pulse wave signals, current filtering methods cannot completely eliminate interference, resulting in fluctuations in the calculated rate of pressure change, thus increasing the difficulty of achieving control accuracy. Summary of the Invention

[0003] In view of this, the present invention provides a method, device, blood pressure monitor and program product for controlling the pressure relief rate of a blood pressure monitor, so as to solve the problems of unstable pressure change rate and increased difficulty in control accuracy caused by pulse wave interference.

[0004] In a first aspect, the present invention provides a method for controlling the pressure relief rate of a blood pressure monitor, comprising: acquiring a pressure signal from the blood pressure monitor; determining the pressure relief rate of the blood pressure monitor based on the change in the pressure signal; determining a pressure relief stage matching the pressure relief rate based on the change in the pressure relief rate; adjusting the opening degree of the electronically controlled valve of the blood pressure monitor according to the control strategy corresponding to the pressure relief stage; and controlling the pressure relief rate based on the opening degree result.

[0005] The pressure relief rate control method for a blood pressure monitor provided in this invention acquires the pressure signal from the blood pressure monitor in real time and dynamically adjusts the pressure relief rate based on its changes. This allows for more precise control of the pressure relief process, improving the accuracy and comfort of the measurement results. Simultaneously, by determining the corresponding pressure relief stage based on the changes in the pressure relief rate and adjusting the opening of the electronically controlled valve, the method ensures a smooth and reasonable pressure relief process, avoiding interference from excessively fast or slow pressure relief rates on the blood pressure measurement results and optimizing the measurement experience.

[0006] In one optional implementation, acquiring the pressure signal from a blood pressure monitor includes: acquiring the original pressure signal from the blood pressure monitor; performing signal processing on the original pressure signal to obtain a pulse signal characterizing the pulse intensity; determining filtering parameters for the original pressure signal based on the intensity corresponding to the pulse signal; and filtering the original pressure signal using the filtering parameters to obtain the pressure signal.

[0007] The pressure relief rate control method for a blood pressure monitor provided in this embodiment of the invention can effectively extract the pulse signal related to the pulse intensity by acquiring and processing the original pressure signal of the blood pressure monitor, and dynamically adjust the filtering parameters according to the intensity of the signal, thereby improving the accuracy and clarity of the original pressure signal.

[0008] In one optional implementation, the filtering parameter is the observation noise; the original pressure signal is filtered using the filtering parameter to obtain the pressure signal, including: acquiring the initial state of the original pressure signal; predicting the signal state of the original pressure signal at different times based on the initial state; determining weighting coefficients based on the predicted signal state and the observation noise; and obtaining the pressure signal based on the predicted signal state and the fusion result of the weighting coefficients and the original pressure signal.

[0009] The pressure relief rate control method for a blood pressure monitor provided in this invention dynamically adjusts the filtering process by combining the initial state and the predicted signal state, accurately predicting the changing trend of the original pressure signal at different time points. By utilizing observed noise to determine weighting coefficients, the true information and noise components of the signal are effectively balanced, thereby achieving fine filtering of the original pressure signal. Therefore, this method can more accurately remove noise, improve signal quality, and make the final pressure signal more stable and reliable, thus improving the accuracy of blood pressure measurement.

[0010] In one optional implementation, the pressure relief stage includes a first stage, a second stage, and a third stage; adjusting the opening of the electronically controlled valve of the sphygmomanometer according to the control strategy corresponding to the pressure relief stage, and controlling the pressure relief rate based on the opening result, includes: when the pressure relief stage is in the first stage, adjusting the opening of the electronically controlled valve using the first control strategy corresponding to the first stage to obtain a first pressure relief rate; wherein, the pressure relief rate in the first stage is zero; when it is determined that the pressure relief stage is in the second stage based on the first pressure relief rate, adjusting the opening of the electronically controlled valve using the second control strategy corresponding to the second stage to obtain a second pressure relief rate; when it is determined that the pressure relief stage is in the third stage based on the second pressure relief rate, adjusting the opening of the electronically controlled valve using the third control strategy corresponding to the third stage.

[0011] The pressure relief rate control method for a blood pressure monitor provided in this invention divides the pressure relief process into multiple stages and employs different control strategies for each stage. This allows for precise adjustment of the opening of the electronically controlled valve of the blood pressure monitor, thereby achieving a gradual and stable pressure relief process. The first stage sets the pressure relief rate to zero, effectively preventing premature pressure relief and ensuring pressure stability. The second and third stages dynamically adjust the control strategy based on changes in the actual pressure relief rate to adapt to the needs of different stages. Therefore, this method optimizes the pressure relief rate, making blood pressure measurement more accurate while improving patient comfort and the stability of the measurement process.

[0012] In one optional implementation, the opening degree of the electrically controlled valve is adjusted using a first control strategy corresponding to the first stage to obtain a first pressure relief rate, including: obtaining an initial control quantity of the electrically controlled valve; controlling the initial control quantity to decrease sequentially according to a preset threshold within each preset control cycle to obtain a first control quantity corresponding to each preset control cycle; adjusting the opening degree of the electrically controlled valve based on the first control quantity, and monitoring the first pressure relief rate generated during the opening degree adjustment process.

[0013] The pressure relief rate control method for a blood pressure monitor provided in this invention can precisely control the opening change of the electronically controlled valve by gradually reducing the initial control quantity over multiple preset control cycles, making the pressure relief process more stable and controllable. By dynamically adjusting the control quantity based on a preset threshold, the valve opening can be precisely adjusted to ensure that the pressure relief rate in the first stage is within the ideal range, thereby avoiding an overly violent or unstable pressure relief process and improving the accuracy and comfort of blood pressure measurement. Simultaneously, this gradual adjustment method facilitates real-time monitoring and optimization of the pressure relief process, ensuring that the pressure relief rate at each stage meets the measurement requirements, further improving the reliability and consistency of the measurement.

[0014] In one optional implementation, the opening degree of the electrically controlled valve is adjusted using a second control strategy corresponding to the second stage to obtain a second pressure relief rate, including: acquiring the current pressure relief rate corresponding to the second stage and the target pressure relief rate of the sphygmomanometer; determining the speed error between the target pressure relief rate and the current pressure relief rate; determining the current control increment based on the speed error; determining the opening degree control amount of the electrically controlled valve based on the fusion result of the current control increment and the control increment at the previous moment; adjusting the opening degree of the electrically controlled valve according to the opening degree control amount, and monitoring the second pressure relief rate generated during the opening degree adjustment process.

[0015] The blood pressure monitor decompression rate control method provided in this invention monitors and calculates the error between the target decompression rate and the current decompression rate in real time. This allows for precise adjustment of the control increment, ensuring more accurate and responsive adjustment of the electronically controlled valve opening. By integrating the current control increment with the control increment from the previous moment, the control process is smoothed, avoiding excessive fluctuations or unstable adjustments. This ensures that the decompression rate changes steadily according to the predetermined target, thereby improving the measurement accuracy of the blood pressure monitor and enhancing the user experience. It ensures that the decompression process is both accurate and stable, effectively preventing inaccurate measurements caused by excessively fast or slow decompression rates.

[0016] In one optional implementation, the opening degree of the electronically controlled valve is adjusted using a third control strategy corresponding to the third stage, including: performing data fitting on historical pressure relief rate data to obtain fitting parameters; determining the predicted pressure relief rate at any given time based on the fitting parameters, and obtaining the actual pressure relief rate corresponding to any given time; adjusting the opening degree of the electronically controlled valve based on the difference between the predicted pressure relief rate and the actual pressure relief rate until the pressure relief rate of the sphygmomanometer meets the target pressure relief rate.

[0017] The blood pressure monitor decompression rate control method provided in this invention obtains accurate fitting parameters by fitting historical decompression rate data, providing a reliable predictive model for the subsequent decompression process. Feedback adjustment is performed based on the difference between the predicted and actual decompression rates, allowing precise adjustment of the opening of the electronically controlled valve, thereby gradually adjusting the decompression rate to the target value. Therefore, this method effectively combines historical data and real-time feedback, dynamically correcting deviations during the decompression process and improving the accuracy and stability of decompression control. Through this adaptive control method, the blood pressure monitor's measurement process not only better meets the expected goals but also maintains good performance under different conditions, ensuring a smooth and accurate decompression process, further enhancing measurement reliability and user experience.

[0018] Secondly, the present invention provides a pressure relief rate control device for a blood pressure monitor, comprising: an acquisition module for acquiring a pressure signal from the blood pressure monitor; a first determination module for determining the pressure relief rate of the blood pressure monitor based on the change in the pressure signal; a second determination module for determining a pressure relief stage matching the pressure relief rate based on the change in the pressure relief rate; and a control module for adjusting the opening degree of the electronically controlled valve of the blood pressure monitor according to the control strategy corresponding to the pressure relief stage, and controlling the pressure relief rate based on the opening degree result.

[0019] Thirdly, the present invention provides a blood pressure monitor, comprising: a memory and a processor, wherein the memory and the processor are communicatively connected to each other, the memory stores computer instructions, and the processor executes the computer instructions to perform the blood pressure monitor depressurization rate control method of the first aspect or any corresponding embodiment described above.

[0020] Fourthly, the present invention provides a computer-readable storage medium storing computer instructions for causing a computer to execute the pressure relief rate control method of the blood pressure monitor according to the first aspect or any corresponding embodiment thereof.

[0021] Fifthly, the present invention provides a computer program product, including computer instructions for causing a computer to execute the pressure relief rate control method of a blood pressure monitor according to the first aspect or any corresponding embodiment described above. Attached Figure Description

[0022] To more clearly illustrate the specific embodiments of the present invention or the technical solutions in the prior art, the drawings used in the description of the specific embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are some embodiments of the present invention. For those skilled in the art, other drawings can be obtained from these drawings without creative effort.

[0023] Figure 1 This is a schematic flowchart of a method for controlling the pressure relief rate of a blood pressure monitor according to an embodiment of the present invention;

[0024] Figure 2 This is a schematic flowchart of another method for controlling the pressure relief rate of a blood pressure monitor according to an embodiment of the present invention;

[0025] Figure 3 This is a schematic diagram of the original pressure signal according to an embodiment of the present invention;

[0026] Figure 4 This is a schematic diagram of signal processing of the original pressure signal according to an embodiment of the present invention;

[0027] Figure 5 This is a schematic diagram of a pressure signal according to an embodiment of the present invention;

[0028] Figure 6 This is a flowchart illustrating another method for controlling the pressure relief rate of a blood pressure monitor according to an embodiment of the present invention.

[0029] Figure 7 This is a comparison chart of the pressure relief rate calculated directly from the curve of the original pressure signal according to an embodiment of the present invention and the pressure change rate calculated from the curve of the pressure signal after using Kalman filtering.

[0030] Figure 8 This is a schematic diagram showing the calculation results of the pressure relief rate during the pressure reduction process according to an embodiment of the present invention;

[0031] Figure 9 This is a structural block diagram of a pressure relief rate control device for a blood pressure monitor according to an embodiment of the present invention;

[0032] Figure 10 This is a schematic diagram of the hardware structure of a blood pressure monitor according to an embodiment of the present invention. Detailed Implementation

[0033] To make the objectives, technical solutions, and advantages of the embodiments of the present invention clearer, the technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0034] In the application of electronic blood pressure monitors, the depressurization measurement method has become the mainstream due to its high consistency with the traditional mercury auscultation method and low signal interference. The depressurization rate is a key factor in ensuring the accuracy and comfort of blood pressure measurement, directly affecting the measurement results of the Korotkoff sound auscultation method and the oscillometric method. The standard recommended depressurization rate is 3 mmHg / second; excessively rapid depressurization may increase measurement error. Traditional mechanical depressurization valves may cause unstable depressurization rates in different usage scenarios, thus affecting measurement accuracy, especially when the arm's size changes significantly or pressure varies considerably. To solve this problem, electronically controlled depressurization valves are used in electronic blood pressure monitors.

[0035] Compared to mechanical pressure relief valves, electrically controlled valves offer significant advantages in control freedom and adaptability, but their performance relies heavily on high-quality pressure relief control algorithms. Improper control can lead to unstable pressure reduction processes, even less precise than mechanical valves. Pulse wave signal interference is a major challenge in controlling the electrically controlled valves of electronic blood pressure monitors. It superimposes on the cuff pressure signal, causing fluctuations in the rate of pressure change, which in turn affects the stability of the control algorithm. Accurately calculating the rate of pressure change requires smoothing and filtering the raw data, but variations in pulse wave signals and individual differences complicate filter design. Currently, filters cannot completely eliminate nonlinear and time-varying interference, so the pressure rate in the input data still fluctuates, increasing the difficulty of the control algorithm. Common filtering methods include low-pass filters based on frequency domain transformation and mathematical methods (such as Kalman filtering). The latter is suitable for scenarios with high real-time requirements, but its filtering effect on time-varying signals is limited. Regarding control algorithms, blood pressure monitors typically use PWM signals and PID control algorithms to regulate the electrically controlled valves, but because pulse interference cannot be completely filtered out, the input data fluctuates significantly, making it difficult for PID control to achieve ideal accuracy.

[0036] In view of this, the technical solution of the present invention acquires the pressure signal from the sphygmomanometer and calculates the pressure relief rate based on the pressure change. Then, based on the change in the pressure relief rate, the corresponding pressure relief stage is determined, and an appropriate control strategy is selected according to the stage to adjust the opening of the electronically controlled valve of the sphygmomanometer. Finally, by adjusting the opening, the pressure relief rate is precisely controlled to achieve a precise pressure relief process.

[0037] According to an embodiment of the present invention, a method for controlling the depressurization rate of a blood pressure monitor is provided. It should be noted that the steps shown in the flowchart in the accompanying drawings can be executed in a computer system such as a set of computer-executable instructions. Furthermore, although a logical order is shown in the flowchart, in some cases, the steps shown or described may be executed in a different order than that shown here.

[0038] This embodiment provides a method for controlling the pressure relief rate of a blood pressure monitor, which can be used in blood pressure monitors. Figure 1 This is a flowchart of a method for controlling the pressure relief rate of a blood pressure monitor according to an embodiment of the present invention, as shown below. Figure 1 As shown, the process includes the following steps:

[0039] Step S101: Obtain the pressure signal from the blood pressure monitor.

[0040] A pressure signal is a processed numerical value representing the pressure in the cuff or bladder measured by an internal sensor of the sphygmomanometer. It characterizes the pressure changes that occur during measurement. Specifically, the pressure sensor monitors the pressure in the cuff in real time and converts it into an electrical signal. After processing, this signal is used to calculate the depressurization rate and control the depressurization process of the sphygmomanometer. In practice, the pressure sensor is installed in the cuff section of the sphygmomanometer to ensure accurate capture of pressure changes within the cuff.

[0041] Step S102: Determine the depressurization rate of the sphygmomanometer based on the change in the pressure signal.

[0042] The change in pressure signal refers to the magnitude of the pressure signal acquired by the pressure sensor inside the sphygmomanometer as a function of time; that is, the increase or decrease in pressure value over a period of time. The rate of pressure release refers to the rate at which the pressure inside the sphygmomanometer cuff decreases, which can be expressed as the rate of pressure change. Specifically, by acquiring the pressure signal collected in real time by the pressure sensor and calculating its change over short time intervals (such as pressure change per second), this change reflects the rate of pressure decrease, thus allowing the calculation of the current rate of pressure release. A faster change in pressure signal indicates a higher rate of pressure release; a slower change indicates a lower rate of pressure release.

[0043] Step S103: Based on the change in the pressure relief rate, determine the pressure relief stage that matches the pressure relief rate.

[0044] The pressure relief phase refers to the process of depressurizing a sphygmomanometer, which is divided into several stages based on the rate of pressure relief. Each stage has different characteristics and control strategies. Specifically, based on the change in the rate of pressure relief, the pressure relief process can be divided into multiple stages, such as a rapid adjustment stage, a controllable stage, and a stable stage. By monitoring changes in the rate of pressure relief, the current stage of pressure relief can be determined, and appropriate control strategies can be selected based on the characteristics of each stage.

[0045] Step S104: Adjust the opening degree of the electronically controlled valve of the sphygmomanometer according to the control strategy corresponding to the pressure relief stage, and control the pressure relief rate based on the opening degree result.

[0046] The opening result refers to the degree or value of the opening of the electrically controlled valve, i.e., the size of the valve opening. Specifically, depending on the different stages of pressure relief, the opening of the electrically controlled valve is adjusted through a control strategy to regulate the pressure relief rate. For example, in the initial pressure relief stage, when a rapid pressure reduction is needed, the opening of the electrically controlled valve is larger, allowing gas to be released more quickly; while as the pressure relief rate slows down and enters a stable stage, the opening will decrease to ensure a more stable pressure drop and avoid the impact of excessively fast or slow pressure relief on blood pressure measurement. In this way, the opening of the electrically controlled valve is precisely adjusted according to the control requirements of different pressure relief stages, thereby achieving fine control of the pressure relief rate and ensuring the accuracy and safety of blood pressure measurement.

[0047] The pressure relief rate control method for a blood pressure monitor provided in this invention acquires the pressure signal from the blood pressure monitor in real time and dynamically adjusts the pressure relief rate based on its changes. This allows for more precise control of the pressure relief process, improving the accuracy and comfort of the measurement results. Simultaneously, by determining the corresponding pressure relief stage based on the changes in the pressure relief rate and adjusting the opening of the electronically controlled valve, the method ensures a smooth and reasonable pressure relief process, avoiding interference from excessively fast or slow pressure relief rates on the blood pressure measurement results and optimizing the measurement experience.

[0048] This embodiment provides a method for controlling the pressure relief rate of a blood pressure monitor, which can be used in blood pressure monitors. Figure 2 This is a flowchart of a method for controlling the pressure relief rate of a blood pressure monitor according to an embodiment of the present invention, as shown below. Figure 2 As shown, the process includes the following steps:

[0049] Step S201: Obtain the pressure signal from the blood pressure monitor.

[0050] Specifically, step S201 includes:

[0051] Step S2011: Obtain the raw pressure signal from the blood pressure monitor.

[0052] The raw pressure signal refers to the initial pressure data inside the cuff detected and collected by the pressure sensor inside the blood pressure monitor. Specifically, the main control chip of the blood pressure monitor periodically collects data from the pressure sensor at a set sampling rate (e.g., 100Hz). This data is raw data without any processing or filtering and directly reflects the real-time pressure changes inside the cuff.

[0053] Step S2012: Perform signal processing on the original pressure signal to obtain a pulse signal used to characterize the pulse intensity.

[0054] A pulse signal is a signal extracted from a raw pressure signal through signal processing that effectively describes the intensity of pulse fluctuations. Specifically, data is extracted from the raw pressure signal (raw pressure data) at set time intervals (e.g., 0.1 seconds). This can also be understood as segmenting the raw data into time series segments to obtain a set of timed sampled data, such as... Figure 3 As shown. Next, the extracted data undergoes four-point differential processing. The purpose of four-point differential is to remove low-frequency components from the signal and highlight the high-frequency fluctuations related to the pulse by calculating the difference between the current pressure value and the pressure values ​​at four previous sampling points. The differential formula is as follows:

[0055]

[0056] Where Ds1(n) is the differential data, Dp1(n) is the pressure data at the current moment, and Dp1(n-4) is the pressure data before the four sampling points.

[0057] After performing four-point differential analysis, a second differential analysis is performed to eliminate baseline drift in the signal and further enhance the high-frequency components of the pulse signal. The purpose of the second differential analysis is to eliminate any slow-changing components that may exist in the first differential analysis, bringing the signal baseline to zero. The formula for the second differential analysis is as follows:

[0058] Ds2(n)=Ds1(n)-Ds1(n-1)

[0059] Where Ds2(n) is the data after the second difference, and Ds1(n) and Ds1(n-1) are the four-point difference data of the current time and the previous time, respectively.

[0060] For the quadratic difference signal Ds2(n), its absolute value is taken to remove negative values, retaining only the amplitude information of the pulse fluctuation. Finally, conditional exponential smoothing is applied to the signal Ds3(n) after absolute value to obtain the smoothed signal S(n). The purpose of smoothing is to remove high-frequency noise from the signal, making the pulse signal more stable and easier for subsequent analysis. The smoothing process uses a conditional smoothing factor k, which is determined by the magnitude of the current value and the previous value: if Ds3(n) ≥ Ds3(n-1), a larger smoothing factor is used (e.g., k = 0.8); otherwise, a smaller smoothing factor is used (e.g., k = 0.1). The formula for the smoothed signal S(n) is as follows:

[0061] S(n)=k×Ds3(n)+(1-k)×S(n-1)

[0062] The smoothed signal S(n) calculated according to the above formula is the pulse signal used to characterize pulse intensity, such as... Figure 4 As shown.

[0063] Step S2013: Determine the filtering parameters for the original pressure signal based on the intensity corresponding to the pulse signal.

[0064] Filtering parameters refer to the parameters used to filter and process the raw pressure signal. Specifically, the intensity of the pulse signal reflects the amplitude of blood pressure fluctuations. Using this intensity, appropriate filtering parameters can be determined through preset mathematical formulas or algorithms. For example, when the filtering parameter is the observation noise (observation error) in the Kalman filter, the pulse intensity signal S(n) can be used to dynamically adjust the observation noise R in the Kalman filter, with the relationship: R = 10 × S(n), R < 120.

[0065] Step S2014: Filter the original pressure signal using filtering parameters to obtain the pressure signal.

[0066] The filter is adjusted using filtering parameters. The adjusted filter then processes the original pressure signal according to the new filtering parameters to obtain the final pressure signal. Specifically, the filter can be a Kalman filter. The Kalman filter will adjust the filtering parameters (e.g., R = 10 × S(n)) calculated based on the pulse signal S(n). The adjustment of the filtering parameters affects how the filter weights and processes the original pressure signal to obtain the final pressure signal.

[0067] In some optional implementations, the filtering parameter is the observation noise, and step S2014 above includes:

[0068] Step a1: Obtain the initial state of the original pressure signal.

[0069] The initial state is used to characterize the initial state estimate and the initial covariance matrix of the original pressure signal. Specifically, the initial state estimate x(0) represents the state at the initial time, where x(0) = [z(0); 0], z(0) is the initial input pressure (i.e., the pressure value measured by the original pressure signal at time n = 0), and the second component is 0, indicating that the initial velocity or acceleration is zero. The covariance matrix P(0) is used to characterize the uncertainty of the initial state estimate; for example, P(0) can be set to [1, 1; 1, 1].

[0070] Step a2: Based on the initial state, predict the signal state of the original pressure signal at different times.

[0071] Establish the discrete-time state equation: x(n) = A × x(n-1) + B × u. Where x(n) is the prior state estimate at time n; x(n-1) is the state estimate at time n-1; and A and B are the process gain matrices. Specifically, A = [1 / 2 × delta_t; 0 / 1], B = [-1 / 2 × delta_t^2; delta_t], where delta_t is the control period (e.g., 0.2), and u is the control law (which can be understood as a deceleration that does not change with the external control quantity, approximated as a constant, e.g., 2).

[0072] Assuming the original pressure signal follows a normal distribution, the corresponding covariance update equation is: P(n)=A×P(n-1)A'+Q. In the equation, P(n) is the state covariance matrix at time n, P(n-1) is the state covariance matrix at time n-1, and Q is the state process variance matrix (which can be understood as the state update process, for example, [0, 0; 0, 3]).

[0073] After determining the initial state estimate x(0) and the initial covariance matrix P(0), the signal state of the original pressure signal at different times can be calculated based on the discrete-time state equation and the covariance update equation mentioned above.

[0074] Step a3: Determine the weighting coefficients based on the predicted signal state and observation noise.

[0075] In Kalman filtering, the weighting coefficient K(n) is used to balance the degree of fusion between the predicted state and the observed data (the original pressure signal). Specifically, the calculation of the weighting coefficient depends on the predicted covariance matrix P(n) and the observed noise R, and the formula for calculating the weighting coefficient K(n) is:

[0076] K(n)=P(n)×H' / (H×P(n)×H'+R)

[0077] Where H = [1, 0] is the observation matrix, representing how pressure values ​​are extracted from the state estimate; R is the observation noise, representing the uncertainty of the measurement data, which is related to the accuracy of the measuring equipment or the signal quality. R is dynamically adjusted through the pulse signal S(n), i.e., R = 10 × S(n), and the maximum value of R is 120. The higher the intensity of the pulse signal, the greater the observation noise R, thereby reducing the weight of the observation data.

[0078] Step a4: Based on the predicted signal state and the fusion result of the weighting coefficients and the original pressure signal, the pressure signal is obtained.

[0079] Based on the predicted signal state x(n) and weighting coefficients K(n), the Kalman filter updates the system's state estimate by combining the predicted state with the actual observed data (the original pressure signal). The updated state X(n) can be obtained through the following equation:

[0080] X(n)=x(n)+K(n)×(z(n)-H×x(n))

[0081] Where z(n) is the observed value (original pressure signal) at the current moment, H×x(n) is the expected observed value based on the predicted state, and z(n)-H×x(n) is the difference between the observed value and the predicted value.

[0082] The X(n) calculated from the above equation is the filtered pressure signal, such as... Figure 5 As shown. Simultaneously, the covariance matrix P(n) is also updated based on the Kalman gain K(n) to reflect the new uncertainties:

[0083] P(n) = (IK(n) × H)P(n)

[0084] Where I = eye(2) is a 2-vector identity matrix.

[0085] In the above implementation, by combining the initial state and the predicted signal state, the filtering process can be dynamically adjusted to accurately predict the changing trend of the original pressure signal at different time points. By utilizing observed noise to determine the weighting coefficients, the true information and noise components of the signal are effectively balanced, thereby achieving fine filtering of the original pressure signal. Therefore, this method can more accurately remove noise, improve signal quality, and make the final pressure signal more stable and reliable, thus improving the accuracy of blood pressure measurement.

[0086] Step S202: Determine the depressurization rate of the sphygmomanometer based on the change in the pressure signal. For details, please refer to [link to relevant documentation]. Figure 1 Step S102 of the illustrated embodiment will not be described again here.

[0087] Step S203: Based on the change in the depressurization rate, determine the depressurization stage that matches the depressurization rate. For details, please refer to [link to relevant documentation]. Figure 1 Step S103 of the illustrated embodiment will not be described again here.

[0088] Step S204: Adjust the opening degree of the electronically controlled valve of the sphygmomanometer according to the control strategy corresponding to the pressure relief stage, and control the pressure relief rate based on the opening degree result. For details, please refer to [link to relevant documentation]. Figure 1 Step S104 of the illustrated embodiment will not be described again here.

[0089] The pressure relief rate control method for a blood pressure monitor provided in this embodiment of the invention can effectively extract the pulse signal related to the pulse intensity by acquiring and processing the original pressure signal of the blood pressure monitor, and dynamically adjust the filtering parameters according to the intensity of the signal, thereby improving the accuracy and clarity of the original pressure signal.

[0090] This embodiment provides a method for controlling the pressure relief rate of a blood pressure monitor, which can be used in blood pressure monitors. Figure 6 This is a flowchart of a method for controlling the pressure relief rate of a blood pressure monitor according to an embodiment of the present invention, as shown below. Figure 6 As shown, the process includes the following steps:

[0091] Step S301: Acquire the pressure signal from the blood pressure monitor. For details, please refer to [link to relevant documentation]. Figure 2 Step S201 of the illustrated embodiment will not be described again here.

[0092] Step S302: Determine the depressurization rate of the sphygmomanometer based on the change in the pressure signal.

[0093] The original pressure signal is processed using a filtering method (such as Kalman filtering) to obtain the filtered pressure signal X(n). Based on this filtered pressure signal, the rate of pressure change at each moment is calculated, which is expressed by the formula:

[0094] V1(n)=(X(n)-X(n-1)) / delta_t

[0095] Where X(n) is the pressure value at time n, delta_t is the preset sampling time interval, and V1(n) is the pressure relief rate of the sphygmomanometer at time n.

[0096] Furthermore, a comparison chart is shown between the pressure relief rate calculated directly from the curve of the original pressure signal and the pressure change rate calculated from the curve of the pressure signal after Kalman filtering. Figure 7 As shown.

[0097] Step S303: Based on the change in the pressure relief rate, determine the pressure relief stage that matches the pressure relief rate. For details, please refer to [link to relevant documentation]. Figure 2Step S203 of the illustrated embodiment will not be described again here.

[0098] Step S304: Adjust the opening degree of the electronically controlled valve of the sphygmomanometer according to the control strategy corresponding to the pressure relief stage, and control the pressure relief rate based on the opening degree result.

[0099] Specifically, the depressurization phase includes a first stage, a second stage, and a third stage, and step S304 above includes:

[0100] Step S3041: When the pressure relief stage is in the first stage, the opening degree of the electrically controlled valve is adjusted by the first control strategy corresponding to the first stage to obtain the first pressure relief speed; wherein, the pressure relief speed in the first stage is zero.

[0101] The first stage (rapid adjustment zone) is the initial stage of the blood pressure monitor's depressurization process. At this point, the depressurization rate is 0, meaning there is no gas leakage. The main purpose of this stage is to quickly adjust the control quantity, allowing the blood pressure monitor to rapidly transition from a completely leak-free state to the state where depressurization begins. The first control strategy refers to the specific control method adopted in the first stage, based on the needs of the depressurization process. Specifically, when the depressurization stage is in the first stage, the opening of the electronically controlled valve is adjusted according to the preset first control strategy, and the depressurization rate, i.e., the first depressurization rate, is monitored in real time.

[0102] In some optional implementations, step S3041 above includes:

[0103] Step b1: When the pressure relief stage is in the first stage, obtain the initial control quantity of the electrically controlled valve.

[0104] The initial control value refers to the setpoint when the electrically controlled valve is fully closed. This value keeps the valve at its minimum opening, i.e., fully closed, thus ensuring no gas leakage initially. Specifically, in the first stage of the depressurization process, the control value of the electrically controlled valve is set to a large value (e.g., 80) to keep it closed, at which point there is no gas leakage. Because the electrically controlled valve is closed during this stage, both the leakage rate and the pressure change rate are zero.

[0105] Step b2: Within each preset control cycle, the initial control quantity is decreased sequentially according to a preset threshold to obtain the first control quantity corresponding to each preset control cycle.

[0106] During the rapid adjustment phase (first stage) of the depressurization process, the electrically controlled valve needs to be gradually switched from a closed state to a leaking state by rapidly adjusting the control quantity. In this stage, within each control cycle (delta_t), the control quantity is gradually reduced according to a preset threshold (e.g., 1), causing the valve opening to gradually increase, thereby initiating depressurization, thus obtaining the first control quantity corresponding to each preset control cycle.

[0107] Step b3: Adjust the opening degree of the electrically controlled valve based on the first control quantity, and monitor the first pressure relief rate generated during the opening degree adjustment process.

[0108] The opening of the electrically controlled valve is adjusted based on the first control variable (i.e., the adjusted control variable). Changes in the valve opening directly affect the depressurization rate (i.e., the rate of pressure change). Specifically, the depressurization rate of the gas can be controlled by adjusting the opening. During the adjustment process, it is necessary to monitor the first depressurization rate (i.e., the depressurization rate generated after each change in the control variable) to ensure that the gas depressurization process proceeds smoothly and to avoid depressurization that is too fast or too slow, leading to pressure fluctuations or instability.

[0109] In addition, the duration of the current control variable, CtrolTime, is monitored, and the first depressurization speed data is saved to the array Speed1, which has a length of 4. Whenever the control variable changes, CtrolTime is reset to zero.

[0110] In the above embodiments, by gradually reducing the initial control quantity over multiple preset control cycles, the opening change of the electronically controlled valve can be precisely controlled, making the pressure relief process more stable and controllable. By dynamically adjusting the control quantity based on a preset threshold, the valve opening can be precisely adjusted to ensure that the pressure relief rate in the first stage is within the ideal range, thereby avoiding an overly drastic or unstable pressure relief process and improving the accuracy and comfort of blood pressure measurement. Simultaneously, this gradual adjustment method facilitates real-time monitoring and optimization of the pressure relief process, ensuring that the pressure relief rate at each stage meets the measurement requirements, further improving the reliability and consistency of the measurement.

[0111] Step S3042: When it is determined that the pressure relief stage is in the second stage based on the first pressure relief rate, the opening degree of the electronically controlled valve is adjusted by the second control strategy corresponding to the second stage to obtain the second pressure relief rate.

[0112] The second stage is the controllable stage (controllable zone). In this stage, to avoid overshoot caused by excessively rapid pressure changes, the adjustment of the control quantity needs to be slowed down. Specifically, the entry into the second stage is determined by monitoring the first pressure relief rate (i.e., the change in the pressure relief rate). Once the second stage is entered, to avoid excessively rapid pressure changes, a second control strategy is adopted. This strategy requires slowing down the adjustment rate, allowing the opening of the electronically controlled valve to be gradually adjusted to a more stable state, thereby smoothly transitioning to the optimal pressure relief rate. In this stage, the opening of the electronically controlled valve will be adjusted according to the second control strategy to obtain a more stable, near-optimal second pressure relief rate, ensuring a smooth pressure relief process for the sphygmomanometer and avoiding sudden pressure fluctuations.

[0113] In some optional implementations, step S3042 above includes:

[0114] Step c1: When it is determined that the pressure relief stage is in the second stage based on the first pressure relief rate, obtain the current pressure relief rate corresponding to the second stage and the target pressure relief rate of the sphygmomanometer.

[0115] When the detected rate change of the first pressure relief speed meets the judgment condition of the controllable stage (second stage), the system enters the controllable stage. The judgment condition for entering the controllable stage is as follows:

[0116] Condition 1: If R > 6, then count > 20; otherwise, count > 15.

[0117] Condition 2: Current speed V2 > 2.5 and speed is increasing (2.5 is set according to the target depressurization speed);

[0118] Condition 3: Speed1(n)+Speed1(n-1)>Speed1(n-2)+Speed1(n-3)+0.4 and Speed1(n)>(Speed1(n-2)+Speed1(n-3)-0.1) / 2+0.4;

[0119] If condition 1 is met (or condition 2 or condition 3), the system enters the controllable stage, where `count` is a counter that starts timing from the beginning of the pressure relief stage and increments by 1 for each control cycle. Upon entering the second stage, the current pressure relief rate and the set target pressure relief rate (e.g., zSet = 5.5) are recorded for subsequent control steps.

[0120] Step c2: Determine the speed error between the target depressurization speed and the current depressurization speed.

[0121] The calculation method for the velocity error e(n) is adjusted based on the observed noise R. Specifically, when R ≤ 6, the velocity error is obtained by calculating the difference between the target depressurization velocity (zSet) and the current depressurization velocity (V1), i.e., e(n) = zSet - V1. When R > 6, a pulse begins to appear. To prevent drastic fluctuations in the calculated velocity due to the influence of the pulse, the integral term e(n) = zSet - speed_mean is adjusted, where speed_mean is the median filter of the four points of V1. Specifically, the proportional term [e(n) - e(n-1)] is changed to [e(n) - e(n-2)] / 2, and the differential term [e(n) - 2e(n-1) + e(n-2)] is changed to [e(n-1) - e(n-3)] / 2.

[0122] Step c3: Determine the current control increment based on the speed error.

[0123] After entering the controllable stage, incremental PID is used for auxiliary adjustment. Incremental PID control is a recursive algorithm that subtracts the control quantity at the current moment from the control quantity at the previous moment, and uses the difference as the new control quantity. The process of incremental PID control can be expressed as follows:

[0124] Δu(n) = Kp × [e(n) - e(n - 1)] + Ki × e(n) + Kd × [e(n) - 2e(n - 1) + e(n - 2)]

[0125] In the formula, e(n) is the speed error at the current moment. The values of parameters Kp, Ki, and Kd are obtained through careful debugging of the actual system. Δu(n) is the current control increment.

[0126] In addition, in order to prevent the control quantity from changing too quickly, certain limitations are required. For example, the limitation range of the increment Δu(n) can be (-1 / 12, 1 / 3).

[0127] Step c4, determine the opening control quantity of the electric control valve based on the fusion result of the current control increment and the control increment at the previous moment.

[0128] After adding the control increment u(n - 1) at the previous moment to the current control increment u(n), the control quantity u(n) at the current moment is obtained. The data of u(n) is scaled to obtain the opening control quantity U(n) of the electric control valve. The scaling formula is as follows:

[0129] U(n) = [u(n) - u_min] / (u_max - u_min) × (U_max - U_min)

[0130] In the formula, u_min and u_max are the minimum and maximum values of the PID calculation control quantity, for example, they can be -5 and 5. U_min and U_max are the minimum and maximum values of the valve control quantity increment, for example, they can be 20 and 80. Among them, u_min and u_max and U_min and U_max are in a mapping relationship. The value of U_min represents a low valve control quantity and the valve is in a fully open state. The value of U_max represents a high valve control quantity and the valve is in a fully closed state.

[0131] Next, make a judgment on U(n) obtained in the previous step:

[0132] When U(n) < U(n - 1), if the control time CtrolTime(n - 1) of the control quantity U(n - 1) < delta_t and e(n) < 2.5, then U(n) = U(n - 1), and the control quantity remains unchanged; otherwise, it is controlled according to the PID calculation control quantity.

[0133] When U(n) = U(n-1), if the control time of the control quantity U(n-1) is CtrolTime(n-1)delta_t, then U(n) is reduced by 1; otherwise, the control quantity is calculated according to PID control.

[0134] Step c5: Adjust the opening of the electrically controlled valve according to the opening control amount, and monitor the second pressure relief rate generated during the opening adjustment process.

[0135] The opening degree of the electrically controlled valve is adjusted according to the U(n) value to make the pressure relief rate close to the target pressure relief speed. At the same time, the second pressure relief speed generated during this process is monitored to ensure that the pressure relief process meets the predetermined target, avoids excessively fast or slow pressure relief, and ensures system stability.

[0136] In the above implementation, by monitoring and calculating the error between the target pressure relief rate and the current pressure relief rate in real time, the control increment can be precisely adjusted, ensuring that the adjustment of the electronically controlled valve opening is more accurate and responsive. By integrating the current control increment with the control increment of the previous moment, the control process is smoothed, avoiding excessive fluctuations or unstable adjustments, ensuring that the pressure relief rate changes steadily according to the predetermined target, thereby improving the measurement accuracy of the blood pressure monitor and enhancing the user experience. This ensures that the pressure relief process is both accurate and stable, effectively avoiding inaccurate measurements caused by excessively fast or slow pressure relief rates.

[0137] Step S3043: When it is determined that the pressure relief stage is in the third stage based on the second pressure relief rate, the opening degree of the electrically controlled valve is adjusted by the third control strategy corresponding to the third stage.

[0138] The third stage is the stabilization stage (steady zone). In this stage, the goal of depressurization is to bring the rate of pressure reduction close to the ideal value and maintain stability, ensuring the blood pressure monitor's depressurization process is accurate and smooth. The third control strategy adjusts the control quantity (i.e., the opening of the electronically controlled valve) based on the current depressurization rate. Specifically, when the second depressurization rate indicates entry into the third stage, the opening of the electronically controlled valve is adjusted according to the preset third control strategy: if the depressurization rate is too fast, the opening of the electronically controlled valve is reduced or kept constant, gradually slowing the depressurization rate and approaching the target rate; if the depressurization rate is too slow, the opening of the electronically controlled valve is increased to accelerate the depressurization rate, thus approaching the target rate more quickly.

[0139] In some optional implementations, step S3043 above includes:

[0140] Step d1 involves fitting the historical depressurization rate data to obtain the fitting parameters.

[0141] When the rate change of the second pressure relief velocity meets the criteria for the stable phase (third phase), the system enters the stable phase. The criteria for entering the stable phase are:

[0142] Condition 1: The situation is currently under control;

[0143] Condition 2: The absolute value of the velocity error at four consecutive points is less than the threshold (e.g., 1);

[0144] Condition 3: e(n)Speed1(n)-Speed1(n-1), that is, the speed difference between the previous moment and the current moment is greater than the error of the current moment, which means that the speed is gradually approaching the target speed and the rate of change is decreasing.

[0145] If conditions 1, 2, and 3 are met, the system enters a stable phase. An initial control cycle range T_min and T_max are set (e.g., T_max is 25, T_min is t_min*CtrolTime(n-1), t_min is 0.5). Then, the pressure velocity trend is predicted based on historical pressure relief velocity data (array Speed1). Since Speed1 contains 4 data points, representing the current pressure velocity value after 0.8 seconds, to predict the velocity after 0.2 seconds in the next cycle in real-time, the prediction method is a binomial fit using the least squares method.

[0146] Step d2: Determine the predicted depressurization rate at any given time based on the fitted parameters, and obtain the actual depressurization rate corresponding to any given time.

[0147] Let the output expression of the polynomial fitting (predicted depressurization rate) be:

[0148] P(x) = a0 + a1×x + a2×x 2 +...+an×x n

[0149] For the input sample data:

[0150] x = [x1, x2, ..., xm] T

[0151] y = [y1, y2, ..., ym] T

[0152] This results in the following error: The smallest, for example, n=2, m=4.

[0153] Furthermore, obtain the actual pressure relief rate Speed1(n) corresponding to any given moment.

[0154] Step d3: Based on the difference between the predicted pressure relief rate and the actual pressure relief rate, adjust the opening of the electronically controlled valve until the pressure relief rate of the sphygmomanometer meets the target pressure relief rate.

[0155] Calculate the difference between the actual pressure relief speed Speed1(n) and the predicted pressure relief speed P(n), that is, the error e(n) = Speed1(n) - P(n).

[0156] Through the polynomial P(x) obtained by fitting, the pressure change speed P(n + 1) at the next moment (i.e., the moment n + 1) can be predicted. e(n + 1) is the prediction error at the next moment, which can be obtained by calculating the difference between the actual pressure relief speed and the predicted speed: e(n + 1) = Speed1(n + 1) - P(n + 1), and Speed1(n + 1) is the actual speed in the next cycle.

[0157] When U(n) < U(n - 1) and both e(n + 1) and e(n) are < 1, if CtrolTime(n - 1) < T_min, then U(n) = U(n - 1), and the control quantity remains unchanged. Otherwise, if T_max ≥ CtrolTime(n - 1) ≥ T_min, control is performed according to the PID calculation of the control quantity.

[0158] When U(n) = U(n - 1) and both e(n + 1) and e(n) are ≥ 1, if CtrolTime(n - 1) ≥ T_max, then U(n) is decreased by 1. Otherwise, if T_max ≥ CtrolTime(n - 1) ≥ T_min, control is performed according to the PID calculation of the control quantity.

[0159] At the same time, after each control cycle ends, T_min is updated to t_min × mean(CtrolTime), and T_max is updated to t_max × mean(CtrolTime). In this example, t_max is 1.6, and mean(CtrolTime) is the average of the control times in the past four cycles.

[0160] When U(n) < U(n - 1) and CtrolTime(n - 1) ≥ T_max, if either e(n) or e(n + 1) is less than 0.5, it means that the control cycle setting is too small. At this time, T_max is increased by 1, and U(n) remains unchanged.

[0161] When U(n) = U(n - 1) and T_min ≤ CtrolTime(n - 1), if either e(n) or e(n + 1) is greater than 1, it means that the control cycle setting is too large. At this time, T_min is decreased by 1, and U(n) is decreased by 1.

[0162] Repeat the above pressure filtering and control steps until the pressure reduction process ends, where the calculation results of the pressure relief speed in the pressure reduction process are as shown in the appendix Figure 8 as follows.

[0163] The pressure relief rate control method for a blood pressure monitor provided in this invention divides the pressure relief process into multiple stages and employs different control strategies for each stage. This allows for precise adjustment of the opening of the electronically controlled valve of the blood pressure monitor, thereby achieving a gradual and stable pressure relief process. The first stage sets the pressure relief rate to zero, effectively preventing premature pressure relief and ensuring pressure stability. The second and third stages dynamically adjust the control strategy based on changes in the actual pressure relief rate to adapt to the needs of different stages. Therefore, this method optimizes the pressure relief rate, making blood pressure measurement more accurate while improving patient comfort and the stability of the measurement process.

[0164] This embodiment also provides a pressure relief rate control device for a blood pressure monitor, which is used to implement the above embodiments and preferred embodiments; details already described will not be repeated. As used below, the term "module" can refer to a combination of software and / or hardware that performs a predetermined function. Although the devices described in the following embodiments are preferably implemented in software, hardware implementation, or a combination of software and hardware, is also possible and contemplated.

[0165] This embodiment provides a pressure relief rate control device for a blood pressure monitor, such as... Figure 9 As shown, it includes:

[0166] Acquisition module 401 is used to acquire the pressure signal from the blood pressure monitor;

[0167] The first determining module 402 is used to determine the depressurization rate of the sphygmomanometer based on the change in the pressure signal.

[0168] The second determining module 403 is used to determine the pressure relief stage that matches the pressure relief rate based on the change in pressure relief rate;

[0169] The control module 404 is used to adjust the opening degree of the electronically controlled valve of the sphygmomanometer according to the control strategy corresponding to the pressure relief stage, and to control the pressure relief rate based on the opening degree result.

[0170] In some optional implementations, the acquisition module 401 includes:

[0171] The acquisition submodule is used to acquire the raw pressure signal from the blood pressure monitor;

[0172] The signal processing submodule is used to process the raw pressure signal to obtain a pulse signal that characterizes the pulse intensity.

[0173] The determination submodule is used to determine the filtering parameters for the original pressure signal based on the intensity corresponding to the pulse signal;

[0174] The filtering submodule is used to filter the original pressure signal using filtering parameters to obtain the pressure signal.

[0175] In some optional implementations, the filtering submodule includes:

[0176] The first acquisition unit is used to acquire the initial state of the original pressure signal;

[0177] The prediction unit is used to predict the signal state of the original pressure signal at different times based on the initial state.

[0178] The first determining unit is used to determine the weighting coefficients based on the predicted signal state and observation noise.

[0179] The second determining unit is used to obtain the pressure signal based on the predicted signal state and the fusion result of the weighting coefficients and the original pressure signal.

[0180] In some alternative implementations, the control module 404 includes:

[0181] The first regulating submodule is used to adjust the opening of the electrically controlled valve according to the first control strategy corresponding to the first stage when the pressure relief stage is in the first stage, so as to obtain the first pressure relief rate; wherein, the pressure relief rate in the first stage is zero;

[0182] The second adjustment submodule is used to adjust the opening of the electronically controlled valve by adopting the second control strategy corresponding to the second stage when the pressure relief stage is determined to be in the second stage based on the first pressure relief rate, so as to obtain the second pressure relief rate.

[0183] The third adjustment submodule is used to adjust the opening degree of the electrically controlled valve by adopting the third control strategy corresponding to the third stage when the pressure relief stage is determined to be in the third stage based on the second pressure relief rate.

[0184] In some alternative implementations, the first adjustment submodule includes:

[0185] The second acquisition unit is used to acquire the initial control quantity of the electrically controlled valve;

[0186] The control unit is used to control the initial control quantity to decrease sequentially according to a preset threshold within each preset control cycle, so as to obtain the first control quantity corresponding to each preset control cycle.

[0187] The first regulating unit is used to regulate the opening degree of the electrically controlled valve based on the first control quantity and to monitor the first pressure relief rate generated during the opening degree regulation process.

[0188] In some alternative implementations, the second adjustment submodule includes:

[0189] The third acquisition unit is used to acquire the current pressure relief rate and the target pressure relief rate of the sphygmomanometer corresponding to the second stage.

[0190] The third determining unit is used to determine the speed error between the target depressurization speed and the current depressurization speed;

[0191] The fourth determining unit is used to determine the current control increment based on the speed error;

[0192] The fifth determining unit is used to determine the opening control quantity of the electrically controlled valve based on the fusion result of the current control increment and the control increment at the previous moment;

[0193] The second regulating unit is used to regulate the opening of the electrically controlled valve according to the opening control quantity and monitor the second pressure relief rate generated during the opening regulation process.

[0194] In some optional implementations, the third adjustment submodule includes:

[0195] The fitting unit is used to fit historical depressurization rate data to obtain fitting parameters.

[0196] The sixth determining unit is used to determine the predicted pressure relief rate at any given time based on the fitted parameters, and to obtain the actual pressure relief rate corresponding to any given time.

[0197] The third adjustment unit is used to adjust the opening of the electronically controlled valve based on the difference between the predicted pressure relief rate and the actual pressure relief rate, until the pressure relief rate of the sphygmomanometer meets the target pressure relief rate.

[0198] Further functional descriptions of the above modules and units are the same as those in the corresponding embodiments described above, and will not be repeated here.

[0199] In this embodiment, the pressure relief rate control device of the blood pressure monitor is presented in the form of a functional unit. Here, a unit refers to an ASIC (Application Specific Integrated Circuit) circuit, a processor and memory that execute one or more software or fixed programs, and / or other devices that can provide the above functions.

[0200] The pressure relief rate control device for a blood pressure monitor provided in this invention acquires the pressure signal from the blood pressure monitor in real time and dynamically adjusts the pressure relief rate based on its changes. This allows for more precise control of the pressure relief process, improving the accuracy and comfort of the measurement results. Simultaneously, by determining the corresponding pressure relief stage based on the changes in the pressure relief rate and adjusting the opening of the electronically controlled valve, the device ensures a smooth and reasonable pressure relief process, avoiding interference from excessively fast or slow pressure relief rates on the blood pressure measurement results and optimizing the measurement experience.

[0201] This invention also provides a blood pressure monitor having the above-described features. Figure 9 The pressure relief rate control device of the blood pressure monitor shown.

[0202] Please see Figure 10 , Figure 10This is a schematic diagram of the structure of a blood pressure monitor provided in an optional embodiment of the present invention, such as... Figure 10 As shown, the blood pressure monitor includes one or more processors 10, a memory 20, and interfaces for connecting the various components, including high-speed and low-speed interfaces. The various components communicate with each other via different buses and can be mounted on a common motherboard or otherwise as required. The processor can process instructions executed within the blood pressure monitor, including instructions stored in or on the memory to display graphical information of a GUI on an external input / output device (such as a display device coupled to the interface). In some alternative embodiments, multiple processors and / or multiple buses can be used with multiple memories and multiple storage devices, if desired. Similarly, multiple blood pressure monitors can be connected, each device providing some of the necessary operations (e.g., as a server array, a set of blade servers, or a multiprocessor system). Figure 10 Take a processor 10 as an example.

[0203] Processor 10 may be a central processing unit, a network processor, or a combination thereof. Processor 10 may further include a hardware chip. The hardware chip may be an application-specific integrated circuit (ASIC), a programmable logic device (PLD), or a combination thereof. The programmable logic device may be a complex programmable logic device (CAMP), a field-programmable gate array (FPGA), a general-purpose array logic (GDA), or any combination thereof.

[0204] The memory 20 stores instructions executable by at least one processor 10 to cause at least one processor 10 to perform the method shown in the above embodiments.

[0205] The memory 20 may include a program storage area and a data storage area. The program storage area may store the operating system and applications required for at least one function; the data storage area may store data created based on the use of the blood pressure monitor, etc. Furthermore, the memory 20 may include high-speed random access memory and may also include non-transient memory, such as at least one disk storage device, flash memory device, or other non-transient solid-state storage device. In some alternative embodiments, the memory 20 may optionally include memory remotely located relative to the processor 10, which can be connected to the blood pressure monitor via a network. Examples of such networks include, but are not limited to, the Internet, corporate intranets, local area networks, mobile communication networks, and combinations thereof.

[0206] The memory 20 may include volatile memory, such as random access memory; the memory may also include non-volatile memory, such as flash memory, hard disk or solid-state drive; the memory 20 may also include a combination of the above types of memory.

[0207] The blood pressure monitor also includes an input device 30 and an output device 40. The processor 10, memory 20, input device 30, and output device 40 can be connected via a bus or other means. Figure 10 Taking the example of a connection between China and Israel via a bus.

[0208] Input device 30 can receive input numerical or character information, and generate key signal inputs related to user settings and function control of the blood pressure monitor, such as a touchscreen, keypad, mouse, trackpad, touchpad, indicator, one or more mouse buttons, trackball, joystick, etc. Output device 40 may include a display device, auxiliary lighting device (e.g., LED), and haptic feedback device (e.g., vibration motor), etc. The aforementioned display device includes, but is not limited to, liquid crystal displays, light-emitting diodes, displays, and plasma displays. In some alternative embodiments, the display device may be a touchscreen.

[0209] This invention also provides a computer-readable storage medium. The methods described above according to embodiments of the invention can be implemented in hardware or firmware, or implemented as computer code that can be recorded on a storage medium, or implemented as computer code downloaded via a network and originally stored on a remote storage medium or a non-transitory machine-readable storage medium and then stored on a local storage medium. Thus, the methods described herein can be processed by software stored on a storage medium using a general-purpose computer, a dedicated processor, or programmable or dedicated hardware. The storage medium can be a magnetic disk, optical disk, read-only memory, random access memory, flash memory, hard disk, or solid-state drive, etc.; further, the storage medium can also include combinations of the above types of memory. It is understood that computers, processors, microprocessor controllers, or programmable hardware include storage components capable of storing or receiving software or computer code, which, when accessed and executed by the computer, processor, or hardware, implements the methods shown in the above embodiments.

[0210] A portion of this invention can be applied as a computer program product, such as computer program instructions, which, when executed by a computer, can invoke or provide the methods and / or technical solutions according to the invention through the operation of the computer. Those skilled in the art will understand that the forms in which computer program instructions exist in a computer-readable medium include, but are not limited to, source files, executable files, installation package files, etc. Correspondingly, the ways in which computer program instructions are executed by a computer include, but are not limited to: the computer directly executing the instructions, or the computer compiling the instructions and then executing the corresponding compiled program, or the computer reading and executing the instructions, or the computer reading and installing the instructions and then executing the corresponding installed program. Here, the computer-readable medium can be any available computer-readable storage medium or communication medium accessible to a computer.

[0211] Although embodiments of the invention have been described in conjunction with the accompanying drawings, those skilled in the art can make various modifications and variations without departing from the spirit and scope of the invention, and such modifications and variations all fall within the scope defined by the appended claims.

Claims

1. A method for controlling the pressure relief rate of a blood pressure monitor, characterized in that, The method includes: Acquiring a pressure signal from a blood pressure monitor includes: acquiring the raw pressure signal from the blood pressure monitor; performing signal processing on the raw pressure signal to obtain a pulse signal characterizing pulse intensity; determining filtering parameters for the raw pressure signal based on the intensity corresponding to the pulse signal; the filtering parameters being observation noise; and filtering the raw pressure signal using the filtering parameters to obtain the pressure signal, including: acquiring the initial state of the raw pressure signal; predicting the signal state of the raw pressure signal at different times based on the initial state; determining weighting coefficients based on the predicted signal state and the observation noise; and obtaining the pressure signal based on the predicted signal state and the fusion result of the weighting coefficients and the raw pressure signal. The decompression rate of the blood pressure monitor is determined based on the change in the pressure signal. Based on the change in the pressure relief rate, determine the pressure relief stage that matches the pressure relief rate; The opening degree of the electronically controlled valve of the blood pressure monitor is adjusted according to the control strategy corresponding to the pressure relief stage, and the pressure relief rate is controlled based on the opening degree result.

2. The method according to claim 1, characterized in that, The pressure relief phase includes a first phase, a second phase, and a third phase; adjusting the opening degree of the electronically controlled valve of the blood pressure monitor according to the control strategy corresponding to the pressure relief phase, and controlling the pressure relief rate based on the opening degree result, includes: When the pressure relief stage is in the first stage, the opening degree of the electrically controlled valve is adjusted using the first control strategy corresponding to the first stage to obtain the first pressure relief rate; wherein, the pressure relief rate in the first stage is zero; When it is determined that the pressure relief stage is in the second stage based on the first pressure relief rate, the opening degree of the electrically controlled valve is adjusted using the second control strategy corresponding to the second stage to obtain the second pressure relief rate; When the pressure relief stage is determined to be in the third stage based on the second pressure relief rate, the opening degree of the electrically controlled valve is adjusted using the third control strategy corresponding to the third stage.

3. The method according to claim 2, characterized in that, The step of adjusting the opening degree of the electrically controlled valve using the first control strategy corresponding to the first stage to obtain the first pressure relief rate includes: Obtain the initial control quantity of the electrically controlled valve; Within each preset control cycle, the initial control quantity is controlled to decrease sequentially according to a preset threshold to obtain the first control quantity corresponding to each preset control cycle; The opening degree of the electrically controlled valve is adjusted based on the first control quantity, and the first pressure relief rate generated during the opening adjustment process is monitored.

4. The method according to claim 2, characterized in that, The step of adjusting the opening degree of the electrically controlled valve using the second control strategy corresponding to the second stage to obtain the second pressure relief rate includes: Obtain the current pressure relief rate corresponding to the second stage and the target pressure relief rate of the blood pressure monitor; Determine the speed error between the target depressurization rate and the current depressurization rate; The current control increment is determined based on the speed error; Based on the fusion result of the current control increment and the control increment at the previous moment, the opening control quantity of the electrically controlled valve is determined; The opening degree of the electrically controlled valve is adjusted according to the opening degree control amount, and the second pressure relief rate generated during the opening degree adjustment process is monitored.

5. The method according to claim 2, characterized in that, The method of adjusting the opening degree of the electrically controlled valve using the third control strategy corresponding to the third stage includes: The historical depressurization rate data were fitted to obtain the fitting parameters. The predicted depressurization rate at any given time is determined based on the fitted parameters, and the actual depressurization rate corresponding to that given time is obtained. Based on the difference between the predicted pressure relief rate and the actual pressure relief rate, the opening of the electronically controlled valve is adjusted until the pressure relief rate of the blood pressure monitor meets the target pressure relief rate.

6. A pressure relief rate control device for a blood pressure monitor, characterized in that, The device includes: The acquisition module is used to acquire the pressure signal from the blood pressure monitor; The first determining module is used to determine the depressurization rate of the blood pressure monitor based on the change in the pressure signal; The second determining module is used to determine a pressure relief stage that matches the pressure relief rate based on the change in the pressure relief rate; The control module is used to adjust the opening degree of the electronically controlled valve of the blood pressure monitor according to the control strategy corresponding to the pressure relief stage, and to control the pressure relief rate based on the opening degree result; The acquisition module includes: The acquisition submodule is used to acquire the raw pressure signal of the blood pressure monitor; The signal processing submodule is used to process the original pressure signal to obtain a pulse signal that characterizes the pulse intensity. The determination submodule is used to determine the filtering parameters for the original pressure signal based on the intensity corresponding to the pulse signal; A filtering submodule is used to filter the original pressure signal using the filtering parameters to obtain the pressure signal. Wherein, the filtering parameter is the observation noise, and the filtering processing submodule includes: The first acquisition unit is used to acquire the initial state of the original pressure signal; A prediction unit is used to predict the signal state of the original pressure signal at different times based on the initial state. The first determining unit is used to determine weighting coefficients based on the predicted signal state and the observed noise; The second determining unit is used to obtain the pressure signal based on the predicted signal state and the fusion result of the weighting coefficient and the original pressure signal.

7. A blood pressure monitor, characterized in that, include: The device includes a memory and a processor, which are communicatively connected to each other. The memory stores computer instructions, and the processor executes the computer instructions to perform the pressure relief rate control method of the sphygmomanometer according to any one of claims 1 to 5.

8. A computer program product, characterized in that, Includes computer instructions for causing a computer to execute the pressure relief rate control method of the sphygmomanometer according to any one of claims 1 to 5.

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