Control method and system for pressing device of balloon breathing machine

Abstract

The invention relates to the technical field of medical instruments, and discloses a control method and system for a pressing device of a balloon breathing machine. The method comprises the steps of setting initial pressing parameters, including pressing force, frequency and duration, of a pressing device according to basic information and assisted respiration information of a user, collecting feedback information, including respiration rhythm parameters and ventilation state parameters, of assisted respiration, calculating inspiration duration and respiration frequency of the user based on the respiration rhythm parameters, the basic information and the feedback information are input into a preset model, the standard value and the reference range of each lung function index are obtained, when the theoretical value of any lung function index does not meet the reference range, the pressing force is adjusted, and the pressing time and the pressing frequency are adjusted. The control accuracy and pertinence of the pressing device are improved, and meanwhile the effectiveness and comfort of assisted breathing are improved.

Description

Technical Field

[0001] This application relates to the technical field of medical devices, and particularly to a control method and system for a balloon ventilator presser. Background Art

[0002] In medical first aid and intensive care, a bag-valve-mask (BVM) is a commonly used respiratory assistance device. Traditional BVMs require medical workers to manually press the balloon to assist patients in breathing. However, manual pressing has many problems such as uneven pressing force, unstable frequency, and easy fatigue, which may affect the breathing effect of patients. With the development of medical technology, automatic pressers have gradually been introduced into BVMs to improve the stability and efficiency of ventilation.

[0003] Similar prior arts include the Chinese patent application with the publication number CN117482345A, which discloses a pressure adjustment method, device, equipment, storage medium, and program product. It acquires the ventilation area data at the end of the ventilation pipeline; determines the breathing type of the user currently using the ventilator according to the ventilation area data; and adjusts the gas pressure output by the ventilator according to the breathing type. This method adjusts the gas pressure based on the user's breathing type. There is also the Chinese patent application with the publication number CN118526681A, which discloses a ventilator and its control method, control device, electronic equipment, and storage medium. It collects the first output pressure value and the first output flow value of the ventilator through a sensor; determines the first pressure value generated by the contraction of the respiratory muscles by the controller according to the first output pressure value and the first output flow value; and adjusts the output pressure and / or output flow of the ventilator by the controller when the first pressure value exceeds the set pressure range generated by the contraction of the respiratory muscles.

[0004] When adjusting the pressure of the ventilator in the above prior arts, only a single influencing factor is considered, and the accuracy is insufficient. Therefore, a control method that can dynamically adjust the pressing parameters according to the real-time feedback information of the patient is needed to improve the use effect and safety of the BVM. Summary of the Invention

[0005] This application provides a control method and system for a balloon ventilator presser to improve the accuracy and pertinence of presser control.

[0006] In a first aspect, this application provides a control method for a balloon ventilator presser, and the method includes: Step 1: Obtain the basic information and assisted breathing information of the user, and set the initial pressing parameters of the presser based on the basic information and assisted breathing information, where the pressing parameters include pressing force, pressing frequency, and pressing duration; Step 2: Collect feedback information for assisted breathing. The feedback information includes respiratory rhythm parameters and ventilation status parameters; Step 3: Calculate the user's inspiratory duration and respiratory frequency based on the respiratory rhythm parameters. Subsequently, adjust the pressing duration based on the inspiratory duration and adjust the pressing frequency based on the respiratory frequency; Step 4: Calculate the theoretical value of each lung function index based on the feedback information. At the same time, input the basic information and feedback information into a preset model to obtain the standard value and reference range of each lung function index; Step 5: Determine whether the theoretical values of all lung function indexes meet the reference range. If not, adjust the pressing force, and repeat Steps 2 to 5 until the assisted breathing is completed.

[0007] Combined with the first aspect, in the first implementation manner of the first aspect of the present application, the assisted breathing information includes the purpose of assisted breathing and the method of assisted breathing.

[0008] Combined with the first aspect, in the second implementation manner of the first aspect of the present application, collect the respiratory rhythm parameters according to the first preset period. The respiratory rhythm parameters include the inspiratory start time. The calculation method of the respiratory frequency is as follows: Step 31: After the start of any collection period, collect the user's inspiratory start time in real time, and calculate the user's first respiratory frequency based on the inspiratory start time; Step 32: Calculate the frequency fluctuation value of any two adjacent respiratory cycles based on the first respiratory frequency; Step 33: Determine whether there are N1 continuously calculated frequency fluctuation values that are all less than or equal to the fluctuation threshold. If so, enter Step 34; if not, enter Step 35; Step 34: Take the average value of the N1 respiratory frequencies as the user's respiratory frequency. Subsequently, determine whether the user's respiratory frequency is between two respiratory grade ranges. If not, take the user's respiratory frequency as the respiratory frequency and end the collection of respiratory rhythm parameters. If so, reduce the fluctuation threshold to generate a new fluctuation threshold, and then return to Step 33; Step 35: Take the average value of all the first respiratory frequencies within the first preset period as the respiratory frequency.

[0009] Combined with the first aspect, in the third implementation manner of the first aspect of the present application, the respiratory rhythm parameters include the expiratory start time. The calculation method of the inspiratory duration is as follows: Obtain the expiratory start time of each respiratory cycle corresponding to the respiratory frequency; Calculate the difference between the expiratory start time and the inspiratory start time of any respiratory cycle, and define it as the first inspiratory duration of any respiratory cycle; Take the average value of the first inspiratory durations of all respiratory cycles corresponding to the respiratory frequency as the inspiratory duration.

[0010] In combination with the first aspect, in the fourth implementation manner of the first aspect of the present application, the lung function indicators include the lung elastic expansion ability and the end-inspiratory stable pressure, and step 5 includes: Step 51, determine whether the theoretical value of the lung elastic expansion ability is less than the reference range corresponding to the lung elastic expansion ability. If so, divide the pressing duration into a first pressing duration stage and a second pressing duration stage; Step 52, obtain the standard value corresponding to the end-inspiratory stable pressure and define it as the first standard value, and set a first pressure greater than the first standard value based on the first standard value; Step 53, increase the pressing force during the first pressing duration stage so that the airway pressure at the beginning of inspiration reaches the first pressure, and during the second pressing duration stage, decrease the pressing force so that the end-inspiratory stable pressure is maintained at the first standard value.

[0011] In combination with the first aspect, in the fifth implementation manner of the first aspect of the present application, the lung function indicators include the gas volume entering the airway per unit time and the inspiratory volume of the inspiratory duration. After step 53, it includes: Obtain the first inspiratory volume at the end of the second pressing duration stage and the first gas volume entering the airway per unit time; When the first gas volume entering the airway per unit time exceeds the preset range or the first inspiratory volume is lower than the reference range corresponding to the inspiratory volume, increase the first pressure, the first pressing duration stage or the first standard value; When the first inspiratory volume is higher than the reference range corresponding to the inspiratory volume, decrease the first pressure, the first pressing duration stage or the first standard value.

[0012] In combination with the first aspect, in the sixth implementation manner of the first aspect of the present application, the first pressure is a preset multiple of the first standard value, and the preset multiple is a positive number greater than 1 and less than 2.

[0013] In combination with the first aspect, in the seventh implementation manner of the first aspect of the present application, a force feedback mechanism is introduced, and the method includes: Install a ceramic thick film sensor at the contact part between the presser and the balloon to real-time monitor the actual pressure value. When there is a difference between the actual pressure value and the pressing force, input the actual pressure value into the PID controller; The PID controller calculates a control signal according to the actual pressure value and the pressing force, and outputs the control signal to the actuator to adjust the output force of the presser so that the output force is maintained at the pressing force.

[0014] In the second aspect, the present application provides a control system for a balloon ventilator presser, and the system includes: an initial setting module, a data acquisition module, a frequency adjustment module, a standard calculation module, and a pressure adjustment module; An initial setting module for obtaining the basic information and assisted breathing information of a user, and setting the initial pressing parameters of the presser based on the basic information and the assisted breathing information, where the pressing parameters include pressing force, pressing frequency, and pressing duration; A data acquisition module for acquiring the feedback information of assisted breathing, where the feedback information includes respiratory rhythm parameters and ventilation status parameters; A frequency adjustment module for calculating the user's inspiratory duration and respiratory frequency according to the respiratory rhythm parameters, and then adjusting the pressing duration based on the inspiratory duration and adjusting the pressing frequency based on the respiratory frequency; A standard calculation module for calculating the theoretical value of each lung function index according to the feedback information. At the same time, inputting the basic information and the feedback information into a preset model to obtain the standard value and reference range of each lung function index; A pressure adjustment module for determining whether the theoretical values of all lung function indexes meet the reference range. If not, adjusting the pressing force.

[0015] Compared with the prior art, the beneficial effects of the technical solution of the present application are at least as follows: 1. By obtaining the basic information and assisted breathing information of the user to set the initial pressing parameters, it is possible to provide personalized breathing assistance for the user according to the individual differences of different users and specific assisted breathing needs. At the same time, dynamically adjusting the pressing parameters according to the collected feedback information of assisted breathing can make the pressing action of the balloon ventilator presser more accurately match the user's breathing needs, improve the effect of assisted breathing, and better meet the breathing support needs of different users in different situations.

[0016] 2. By collecting respiratory rhythm parameters in real time and calculating the respiratory frequency and inspiratory duration, it is ensured that the adjustment of the pressing frequency and pressing duration matches the user's actual respiratory rhythm, which helps to maintain the synchronization of the pressing and the patient's breathing and improve the comfort of assisted breathing.

[0017] 3. By calculating the theoretical values of lung function indexes and comparing them with the standard values and reference ranges, it is possible to comprehensively evaluate the user's lung function status and adjust the pressing force according to the evaluation results, ensuring that the operation of the presser is always in the best state and promoting the recovery and improvement of the user's lung function.

[0018] 4. Introducing a force feedback mechanism, the actual pressure value is monitored in real time through a ceramic thick film sensor, and a control signal is calculated by using a PID controller according to the actual pressure value and the pressing force, and the output force of the presser is adjusted in time, ensuring the accuracy and stability of the pressing and improving the safety and effectiveness of assisted breathing. Description of the Drawings

[0019] To more clearly illustrate the technical solutions of the embodiments of the present invention, the following will briefly introduce the drawings required for the description of the embodiments. Obviously, the drawings in the following description are some embodiments of the present invention. For those of ordinary skill in the art, without creative efforts, other drawings can also be obtained based on these drawings.

[0020] Figure 1 Schematic diagram of the structure of the balloon ventilator in the embodiments of the present application; Figure 2 Schematic diagram of an embodiment of the control method for the balloon ventilator presser in the embodiments of the present application; Figure 3 Schematic diagram of an embodiment of the respiratory rate calculation method in the embodiments of the present application; Figure 4 Schematic diagram of an embodiment of the control system for the balloon ventilator presser in the embodiments of the present application; Among them, 1 is the balloon, 2 is the face mask, and 3 is the oxygen connection tube. Detailed implementation manners

[0021] The embodiments of the present application provide a control method and system for a balloon ventilator presser. The terms "first", "second", "third", "fourth", etc. (if any) in the specification and claims of the present application and the above drawings are used to distinguish similar objects and do not necessarily describe a specific order or sequence. It should be understood that such data can be interchanged under appropriate circumstances so that the embodiments described herein can be implemented in an order other than that illustrated or described herein. In addition, the terms "comprising" or "having" and any variations thereof are intended to cover non-exclusive inclusion. For example, a process, method, system, product, or device that includes a series of steps or units does not necessarily have to be limited to those steps or units clearly listed, but may include other steps or units not clearly listed or inherent to these processes, methods, products, or devices.

[0022] Figure 1 Schematic diagram of a structure of a balloon ventilator, including a balloon 1, a presser (not shown), an oxygen connection tube 3, and a face mask 2. The pressure driving principle is as follows: The balloon ventilator squeezes the balloon through the presser to generate a positive pressure airflow, and sends air or oxygen into the user's lungs; when the balloon is squeezed, the internal gas enters the user's airway through the connection tube, pushing the gas into the lungs to complete the inhalation process; during the exhalation phase, the balloon relaxes, and the gas in the user's lungs is discharged through the one-way valve to avoid gas reflux.

[0023] For ease of understanding, the following describes the specific process of the embodiments of the present application. Please refer to Figure 2, an embodiment of the control method for the balloon ventilator pressor in the embodiments of the present application includes: Step 1, obtain the user's basic information and assisted breathing information, and set the initial pressing parameters of the pressor based on the basic information and assisted breathing information, where the pressing parameters include pressing force, pressing frequency, and pressing duration.

[0024] In a specific embodiment, the assisted breathing information includes the purpose of assisted breathing and the mode of assisted breathing.

[0025] The user's basic information is the basis for personalized assisted breathing. Such information may include, but is not limited to: user age: users of different age groups have different needs for respiratory support. For example, the lung function and breathing patterns of infants and elderly users are significantly different from those of adults; weight and body type: weight and body type affect vital capacity and respiratory resistance, thereby affecting the parameter settings of the pressor; medical history and current condition: for example, whether the user has chronic obstructive pulmonary disease (COPD), asthma, heart failure, etc., these diseases will affect respiratory needs and the operation of the pressor; in addition, other physiological parameters such as gender, height, blood oxygen saturation (SpO2) may also be included.

[0026] The assisted breathing information refers to the specific operation and target information related to the assisted breathing process. Such information may include: purpose of assisted breathing: for example, for the treatment of acute respiratory failure, cardiopulmonary resuscitation, postoperative respiratory support, or for relieving the symptoms of chronic respiratory diseases. Different purposes require different pressing strategies. The modes of assisted breathing include, but are not limited to, invasive ventilation, mask ventilation, nasal mask ventilation, etc. Different ventilation modes have different requirements for the parameter settings of the pressor. By understanding the purpose and mode of assisted breathing, the specific goals of the pressor operation are clarified to ensure that the pressing process meets the treatment requirements.

[0027] Exemplarily, the initial pressing parameters of the pressor can be set based on the user's basic information and assisted breathing information through various means such as empirical formulas, clinical guidelines, expert systems, and physiological models.

[0028] By obtaining the user's basic information and assisted breathing information, initial pressing parameters are set for the pressor to ensure the pertinence and effectiveness of the pressor operation. Through personalized settings, the effect of assisted breathing can be maximized while reducing potential risks to the user.

[0029] Step 2, collect the feedback information of assisted breathing, and the feedback information includes respiratory rhythm parameters and ventilation state parameters.

[0030] Specifically, feedback information refers to data about the user's breathing state and ventilation effect obtained through various sensors and monitoring devices during assisted breathing. Respiratory rhythm parameters include but are not limited to the start time of inspiration, the end time of inspiration, the start time of exhalation, the end time of exhalation, etc. Ventilation state parameters include but are not limited to the amount of gas entering the airway per unit time, the amount of gas discharged from the airway per unit time, the amount of gas inhaled in each breathing cycle (i.e., the inspiratory volume), the amount of gas exhaled in each breathing cycle (i.e., the expiratory volume), the CO2 concentration, the total CO2 amount, the peak inspiratory pressure, the stable pressure at the end of inspiration, the airway pressure at the end of exhalation, etc. Among them, the inspiratory volume can be obtained by integrating the amount of gas entering the airway per unit time based on the duration of inspiration, the expiratory volume can be obtained by integrating the amount of gas discharged from the airway per unit time based on the duration of exhalation, and the total CO2 amount can be obtained by integrating the CO2 concentration based on the duration of exhalation.

[0031] Real-time collection of the user's respiratory rhythm parameters and ventilation status parameters through various sensors and monitoring equipment is the basis for evaluating the effect of assisted breathing and adjusting the compressor parameters. Accurate and timely feedback information is essential for achieving effective assisted breathing. Through continuous monitoring and adjustment, it can ensure that the operation of the compressor is always in the best state, thereby maximizing the effect and safety of assisted breathing.

[0032] Step 3: Calculate the user's inhalation duration and respiratory rate based on the respiratory rhythm parameters, and then adjust the compression duration based on the inhalation duration and adjust the compression frequency based on the respiratory rate.

[0033] The compression duration of the compressor should match the user's inspiratory duration to ensure adequate ventilation support during the inspiratory phase; the compression frequency of the compressor should be synchronized with the user's respiratory rate to achieve effective ventilation support.

[0034] The user's breathing state changes dynamically. By dynamically adjusting the compression parameters, it can adapt to the user's changing breathing needs and ensure the effectiveness of assisted breathing. At the same time, synchronization and adaptive adjustment can improve the user's comfort and reduce breathing discomfort or human-machine confrontation caused by asynchrony between compression and breathing. Through continuous monitoring and adjustment, it can be ensured that the operation of the compressor always matches the user's breathing state, thereby maximizing the effect and safety of assisted breathing. This dynamic adjustment mechanism enables the compressor to adapt to the user's breathing needs at different times and in different states, improving the flexibility and effectiveness of assisted breathing.

[0035] Step 4: Calculate the theoretical value of each lung function index based on the feedback information. At the same time, input the basic information and feedback information into the preset model to obtain the standard value and reference range of each lung function index.

[0036] Specifically, the pulmonary function indicators include, but are not limited to, respiratory resistance, lung volume, pulmonary elastic expansion ability, end-inspiratory steady pressure, the amount of gas entering the airway per unit time, and the inspiratory volume during the inspiratory duration. Among them, respiratory resistance refers to the resistance encountered by air when passing through the airway during breathing; the pulmonary elastic expansion ability measures the ability of the lungs to change volume under a unit pressure change; the end-inspiratory steady pressure reflects the state of the airway pressure at the end of the inspiratory phase and is used to evaluate the expansion state of the alveoli; the amount of gas entering the airway per unit time reflects whether the gas can smoothly enter the lungs and whether the alveoli are fully expanded during the inspiratory phase; the inspiratory volume during the inspiratory duration is used to determine whether there is enough gas entering the lungs during each breath for effective gas exchange. The pulmonary function indicators overlap with the ventilation state parameters.

[0037] The feedback information is an important basis for evaluating the user's pulmonary function status. According to the obtained feedback information and a preset mathematical formula, the theoretical values of the pulmonary function indicators can be calculated, which can provide a reference for medical staff for ventilation support. Exemplarily, the ratio of the amount of gas inhaled in each breathing cycle to the difference between the peak inspiratory pressure and the end-expiratory airway pressure is used as the pulmonary elastic expansion ability value, and the ratio of the expiratory duration to 5 times the pulmonary elastic expansion ability value is used as the respiratory resistance.

[0038] The preset model is a mathematical model established based on a large amount of clinical data and medical research, used to predict and evaluate the user's pulmonary function indicators. By inputting the user's basic information and feedback information into the preset model, the standard values and their reference ranges of each pulmonary function indicator can be obtained. Among them, the standard value refers to the ideal value that a specific pulmonary function indicator should reach under normal circumstances, and the reference range refers to the acceptable fluctuation range of a specific pulmonary function indicator under normal circumstances. Setting a reference range for each pulmonary function indicator to ensure that the pulmonary function indicators are within a safe and effective range, medical staff can monitor the user's assisted breathing state in real time and adjust the assisted breathing parameters in a timely manner to meet the user's needs.

[0039] By calculating the theoretical values of the pulmonary function indicators and combining the standard values and reference ranges generated by the preset model, it provides a scientific basis for the dynamic adjustment of the pressing parameters, which not only helps to improve the effect of assisted breathing, but also enhances the intelligence and safety of the system, provides personalized breathing support for users, and better meets the breathing support needs of different users in different situations.

[0040] Step 5: Determine whether the theoretical values of all pulmonary function indicators meet the reference range. If not, adjust the pressing force and repeat Steps 2 to 5 until the assisted breathing is completed.

[0041] Compare the calculated theoretical values of the lung function indicators with the reference ranges provided by the preset model. If the theoretical values of all lung function indicators meet the reference ranges, it indicates that the current auxiliary respiration parameters are appropriate; otherwise, it indicates that the ventilation effect is not good, and the operating parameters of the pressor need to be adjusted.

[0042] Exemplarily, if the respiratory resistance is higher than the reference range corresponding to the respiratory resistance, it indicates that there may be obstruction or stenosis in the airway, and the pressing force can be appropriately increased; if the lung volume is lower than the reference range corresponding to the lung volume, it indicates that the ventilation volume may be insufficient, and the pressing force can be increased to increase the tidal volume and improve ventilation; if the lung elastic expansion ability is lower than the reference range corresponding to the lung elastic expansion ability, it indicates that it is difficult to expand the alveoli, and the pressing force can be adjusted, and so on.

[0043] Auxiliary respiration is a dynamic process. The user's respiratory state may change over time, treatment effect, or other factors. While adjusting the pressing force, continue to monitor the user's feedback information to evaluate the effect of the adjustment. According to the changes in the user's respiratory state, dynamically adjust the pressing force to adapt to the user's changing respiratory needs. Exemplarily, a prediction model can be used to predict the effects of different pressing force adjustment schemes based on the user's current state and historical data, and further select the pressing force adjustment scheme with the best predicted effect for implementation. According to the user's specific situation (such as age, weight, condition, etc.), formulate a personalized adjustment scheme to ensure that the adjusted pressing force meets the user's actual needs; or, in order to avoid discomfort to the user or ventilator-associated lung injury caused by too large an adjustment amplitude, the adjustment of the pressing force should be carried out step by step. Through small-amplitude, multiple adjustments, the amplitude of each adjustment should be small and controlled within a safe range.

[0044] Continuous monitoring and dynamic adjustment are the keys to ensuring the auxiliary respiration effect. By continuously iterating the above steps in a loop, it is possible to respond in real time to changes in the user's respiratory state and maximize the safety and effectiveness of auxiliary respiration.

[0045] In a specific embodiment, respiratory rhythm parameters are collected according to a first preset period. The respiratory rhythm parameters include the start time of inspiration. The calculation method of the respiratory frequency is as follows: Step 31: After the start of any collection period, collect the user's inspiration start time in real time, and calculate the user's first respiratory frequency based on the inspiration start time.

[0046] Step 32: Calculate the frequency fluctuation value of any two adjacent respiratory cycles based on the first respiratory frequency. Step 33: Determine whether there are N1 continuously calculated frequency fluctuation values that are all less than or equal to the fluctuation threshold. If so, go to Step 34; if not, go to Step 35.

[0047] Step 34, take the average value of N1 breathing frequencies as the user's breathing frequency, then determine whether the user's breathing frequency is between two breathing level ranges. If not, take the user's breathing frequency as the breathing frequency and end the collection of respiratory rhythm parameters. If so, lower the fluctuation threshold to generate a new fluctuation threshold, and then return to step 33.

[0048] Step 35: taking the average value of all first respiratory frequencies within the first preset period as the respiratory frequency.

[0049] A schematic diagram of an embodiment of a method for calculating respiratory frequency is shown in FIG. Figure 3 shown.

[0050] The user's breathing rate is related to his or her age or physical condition. For infants and young children, the breathing rate is faster, and for adults, the breathing rate is slower. The acquisition cycle and N1 are set according to the experience of those skilled in the art or according to the actual application scenario, and the embodiments of the present application do not limit this. For example, for adults, the acquisition cycle is 25 seconds, and an adult can usually complete 5 to 8 complete breaths in 25 seconds, and N1 is set to 2; for infants under 1 year old, the acquisition cycle is 15 seconds, and infants can usually complete 4 to 7 complete breaths in 15 seconds, and N1 is set to 2.

[0051] Taking an adult as an example, the technical solution of this application is explained. The collection cycle is 25 seconds, and a total of 7 complete breathing cycles can be collected, and the quality of the breathing condition is graded based on the breathing frequency. For example, less than 12 times is the first level range (less), 12 to 20 times is the second level range (normal), and more than 20 times is the third level range (more). The fluctuation threshold is set to a second preset multiple of the middle value of the normal range, and the second preset multiple is less than 0.5. Preferably, the second preset multiple is 0.1.

[0052] The user's respiratory rhythm parameters are monitored. The first three first respiratory frequencies are 13, 14, and 13, and their frequency fluctuation values ​​are all 1, that is, there are two consecutive frequency fluctuation values ​​less than the fluctuation threshold. The user's respiratory frequency calculated based on the three values ​​is 13.33, which is within the second level range. The user's respiratory frequency is used as the respiratory frequency and the collection of respiratory rhythm parameters is terminated; the first three first respiratory frequencies are 13, 15, and 14, and their frequency fluctuation values ​​are 2 and 1 respectively, which do not meet the requirements. Continue to monitor the start time of the fourth inhalation; any three consecutive respiratory frequencies are 21, 20, and 20, and their frequency fluctuation values ​​meet the situation that there are two consecutive frequency fluctuation values ​​less than the fluctuation threshold. The user's respiratory frequency calculated based on the three values ​​is 20.33, which is between the second level range and the third level range. The fluctuation threshold is lowered to generate a new fluctuation threshold (for example, the second preset multiple is set to 0.07), and monitoring continues.

[0053] When the user's breathing frequency is between two breathing level ranges, to reduce the risk of misjudgment caused by measurement errors, improve the reliability of calculating the breathing frequency, and thus improve the reliability of the breathing function assessment results and the measurement accuracy of the breathing frequency, the fluctuation threshold is set smaller.

[0054] The user's breathing characteristics are fixed within a certain period of time or change very little. To reduce the computational load, the breathing rhythm parameters of the user are periodically and real-time monitored through sensors or monitoring devices, and the breathing characteristic values are further calculated. When N1 consecutive frequency fluctuation values are all less than or equal to the fluctuation threshold, it indicates that the user's breathing frequency is stable. When the user's breathing frequency is within any breathing level range, the current user's breathing frequency is used as the final breathing frequency, and the acquisition of the breathing rhythm parameters is ended. While quickly obtaining the user's breathing frequency, the computational load can be reduced, the monitoring consumption can be reduced, and the monitoring efficiency can be improved.

[0055] In a specific embodiment, the breathing rhythm parameters include the exhalation start time, and the calculation method of the inhalation duration is as follows: Obtain the exhalation start time of each breathing cycle corresponding to the breathing frequency; Calculate the difference between the exhalation start time and the inhalation start time of any breathing cycle, and define it as the first inhalation duration of any breathing cycle; Take the average value of the first inhalation durations of all breathing cycles corresponding to the breathing frequency as the inhalation duration.

[0056] Specifically, obtaining each breathing cycle corresponding to the breathing frequency is the breathing cycle used when calculating the breathing frequency. For example, if the breathing frequency is calculated based on the breathing rhythm parameters of the first 3 breathing cycles within the acquisition period, the breathing cycles corresponding to the breathing frequency are these first 3 breathing cycles.

[0057] In the traditional ventilator control method, the inhalation duration is usually estimated based on the breathing frequency and a preset inhalation time ratio. This method ignores the individual differences in breathing cycles and may lead to inaccurate calculation of the inhalation duration.

[0058] The technical solution of the present application can directly measure the actual inhalation duration by monitoring respiratory rhythm parameters and calculating the average value of the first inhalation duration of multiple respiratory cycles. This method takes into account the complete process of the respiratory cycle, avoids the error caused by estimation, and significantly improves the calculation accuracy and stability of the inhalation duration. The inhalation duration is an important basis for adjusting the compression duration. By accurately calculating the inhalation duration, it can be ensured that the compression process matches the user's inhalation needs; and the user's breathing state is dynamically changing. The compression parameters are dynamically adjusted according to the user's specific situation to adapt to the user's changing breathing needs. It can respond to changes in the user's breathing state in real time, provide personalized breathing support for different users, improve the flexibility and adaptability of assisted breathing, reduce human-machine confrontation, and improve user comfort and compliance.

[0059] In a specific embodiment, the lung function index includes the lung elastic expansion capacity and the end-inspiratory stable pressure, and step 5 includes: Step 51, determine whether the theoretical value of the lung elastic expansion capacity is less than the reference range corresponding to the lung elastic expansion capacity, and if so, divide the compression duration into a first compression duration stage and a second compression duration stage.

[0060] Step 52: Obtain a standard value corresponding to the stable pressure at the end of inhalation and define it as a first standard value, and set a first pressure greater than the first standard value based on the first standard value.

[0061] Step 53, during the first compression duration phase, the pressing force is increased so that the initial airway pressure of inhalation reaches the first pressure, and during the second compression duration phase, the pressing force is decreased so that the stable pressure at the end of inhalation is maintained at the first standard value.

[0062] In a specific embodiment, the first pressure is a preset multiple of the first standard value, and the preset multiple is a positive number greater than 1 and less than 2.

[0063] Specifically, the duration of the first pressing duration stage is less than 0.5 times of the pressing duration, and the preset multiple is less than 1.35, which is set specifically according to the actual situation of the user.

[0064] The theoretical value of the lung's elastic expansion ability is less than the reference range corresponding to the lung's elastic expansion ability, indicating that the difficulty of expanding the lungs under external force increases, that is, the elasticity of the lungs weakens, and a greater pressure is required to expand the lungs. To prevent over-inflation of the lungs while ensuring the expansion effect of the lungs, the pressing duration is adjusted in segments to adapt to the elastic characteristics of the lungs. In the first pressing duration stage, a first pressure higher than the standard value is provided to the lungs to quickly increase the alveolar pressure, enabling the alveoli to expand more rapidly to overcome the resistance brought about by the decrease in the lung's elastic expansion ability; in the first pressing duration stage, the gas supply is reduced to maintain the airway pressure at the standard value, while promoting the full diffusion of gas between the alveoli and the pulmonary artery, improving the gas exchange efficiency, and improving the user's oxygenation status, avoiding over-expansion and preventing barotrauma.

[0065] By adjusting the pressing duration and pressing force in segments, it is possible to better adapt to the changes in the lung's elastic expansion ability, improve the ventilation effect, ensure that the user obtains sufficient oxygen supply, reduce the work of breathing, and at the same time be able to reduce lung damage caused by over-ventilation or too high airway pressure, improve the treatment safety, and significantly improve the effect and safety of assisted breathing.

[0066] In a specific embodiment, the lung function indicators include the amount of gas entering the airway per unit time and the inspiratory volume during the inspiratory duration. After step 53, it includes: Obtain the first inspiratory volume and the first gas volume entering the airway per unit time at the end of the second pressing duration stage; When the first gas volume entering the airway per unit time exceeds the preset range or the first inspiratory volume is lower than the reference range corresponding to the inspiratory volume, increase the first pressure, the first pressing duration stage, or the first standard value; When the first inspiratory volume is higher than the reference range corresponding to the inspiratory volume, lower the first pressure, the first pressing duration stage, or the first standard value.

[0067] The above preset range is a range equal to 0 or slightly greater than 0.

[0068] Specifically, based on the reference range corresponding to the end-inspiratory steady pressure, the first standard value is adjusted upward or downward.

[0069] At the end of the second pressing duration stage, if the first gas volume entering the airway per unit time does not reach the above preset range, it may mean that the gas does not enter the lungs smoothly, there is residual gas in the airway, the alveoli do not receive sufficient gas supply, cannot expand fully, and even some alveoli collapse, affecting the gas exchange effect. By increasing the first pressure, the duration of the first pressing duration stage, and / or the standard value, it can help overcome the airway resistance and the elastic resistance of the alveoli, enabling the gas to effectively enter the alveoli and making the first gas volume entering the airway per unit time reach the preset range.

[0070] When the first inhalation volume is lower than the reference range corresponding to the inhalation volume, it indicates that the ventilation volume per breath is insufficient, and there may be problems such as increased work of breathing. By increasing the first pressure, the time of the first pressing duration stage, and / or the standard value, the airway pressure is increased to improve the insufficient ventilation condition and ensure that the user obtains sufficient oxygen supply; when the first inhalation volume is higher than the reference range corresponding to the inhalation volume, it indicates that the ventilation volume per breath is excessive, and there may be problems such as hyperventilation. By reducing the first pressure, the time of the first pressing duration stage, and / or the standard value, the airway pressure is reduced to avoid hyperventilation and reduce the potential risk to the user.

[0071] By monitoring and adjusting the gas volume and inhalation volume, and adjusting the pressing force and pressing duration based on these indicators, precise control of the ventilation volume can be achieved, effectively avoiding hyperventilation and insufficient ventilation, ensuring that the ventilation volume is within a safe range, improving the ventilation efficiency of each pressing, reducing the potential risk to the user while ensuring that the user obtains sufficient oxygen supply, and improving the treatment safety.

[0072] In a specific embodiment, a force feedback mechanism is introduced, including: Install a ceramic thick film sensor at the contact part between the presser and the balloon to real-time monitor the actual pressure value. When there is a difference between the actual pressure value and the pressing force, input the actual pressure value into the PID controller; The PID controller calculates the control signal based on the actual pressure value and the pressing force, and outputs the control signal to the actuator to adjust the output force of the presser so that the output force is maintained at the pressing force.

[0073] By installing a ceramic thick film sensor at the contact part between the presser and the balloon, the actual pressure value can be monitored in real time and accurately. Among them, the ceramic thick film sensor has the characteristics of high precision, high stability and strong anti-interference ability, and is suitable for pressure measurement in medical equipment. The sensor is directly embedded inside the pressing head of the presser to form an integrated structure, reducing external interference and improving the stability and accuracy of the measurement; the PID controller dynamically adjusts the output force of the presser according to the difference between the actual pressure value and the set pressing force, making it always close to the set value. This real-time feedback and precise control mechanism significantly improves the pressing accuracy, ensures that each pressing can provide accurate pressure support, avoids insufficient ventilation or hyperventilation caused by pressure fluctuations, and enhances the safety of use.

[0074] The balloon ventilator presser in the technical solution of this application can achieve precise, stable, and uniform pressing operations. The precise control of the pressing force avoids damage to the user's lungs caused by excessive or insufficient force, improving the safety of ventilation; the stable control of the pressing frequency and the ratio of pressing to relaxation time ensures that the user can obtain continuous and effective ventilation support, improving the user's oxygenation status and respiratory function. At the same time, the introduction of a feedback adjustment mechanism further enhances the robustness of the control. Even in the case of changes in the user's condition or minor malfunctions of the device, the pressing parameters can be quickly adjusted to ensure that the pressing effect is not affected.

[0075] The control method for the balloon ventilator presser in the embodiments of this application was described above. Next, the control system for the balloon ventilator presser in the embodiments of this application will be described. Please refer to Figure 4 One embodiment of the control system for the balloon ventilator presser in the embodiments of this application includes: an initial setting module 10, a data acquisition module 20, a frequency adjustment module 30, a standard calculation module 40, and a pressure adjustment module 50.

[0076] The initial setting module 10 is used to obtain the user's basic information and assisted breathing information, and set the initial pressing parameters of the presser based on the basic information and assisted breathing information. Among them, the pressing parameters include pressing force, pressing frequency, and pressing duration.

[0077] The data acquisition module 20 is used to collect the feedback information of assisted breathing. The feedback information includes respiratory rhythm parameters and ventilation status parameters.

[0078] The frequency adjustment module 30 is used to calculate the user's inspiratory duration and respiratory frequency according to the respiratory rhythm parameters, and then adjust the pressing duration based on the inspiratory duration and adjust the pressing frequency based on the respiratory frequency.

[0079] The standard calculation module 40 is used to calculate the theoretical value of each lung function index according to the feedback information. At the same time, the basic information and feedback information are input into a preset model to obtain the standard value and reference range of each lung function index.

[0080] The pressure adjustment module 50 is used to determine whether the theoretical values of all lung function indexes meet the reference range. If not, the pressing force is adjusted.

[0081] Those skilled in the art can clearly understand that for the convenience and simplicity of description, the specific working processes of the above-described system, system, and unit can refer to the corresponding processes in the foregoing method embodiments and will not be elaborated here.

[0082] When the integrated unit is implemented in the form of a software functional unit and sold or used as an independent product, it can be stored in a computer-readable storage medium. Based on this understanding, the technical solution of this application, in essence, or the part that contributes to the prior art, or all or part of this technical solution, can be embodied in the form of a software product. This computer software product is stored in a storage medium and includes several instructions to enable a computer device (which can be a personal computer, a server, or a network device, etc.) to execute all or part of the steps of the methods described in various embodiments of this application. The aforementioned storage medium includes: various media such as USB flash drives, mobile hard disks, read-only memory (ROM), random access memory (RAM), magnetic disks, or optical discs that can store program codes.

[0083] As described above, the above embodiments are only used to illustrate the technical solutions of this application and are not intended to limit them; although this application has been described in detail with reference to the foregoing embodiments, those of ordinary skill in the art should understand that they can still modify the technical solutions described in the foregoing embodiments, or perform equivalent replacements for some of the technical features; and these modifications or replacements do not cause the essence of the corresponding technical solutions to deviate from the spirit and scope of the technical solutions of various embodiments of this application.

Claims

1. A control method for a balloon ventilator compressor, characterized in that, The method includes: Step 1: Obtain the basic information and assisted breathing information of the user, and set the initial pressing parameters of the presser based on the basic information and the assisted breathing information, where the pressing parameters include pressing force, pressing frequency, and pressing duration; Step 2: Collect the feedback information of assisted breathing, where the feedback information includes respiratory rhythm parameters and ventilation state parameters; Step 3: Calculate the inspiratory duration and respiratory frequency of the user based on the respiratory rhythm parameters, and then adjust the pressing duration based on the inspiratory duration and adjust the pressing frequency based on the respiratory frequency; Step 4: Calculate the theoretical value of each lung function index based on the feedback information. At the same time, input the basic information and the feedback information into a preset model to obtain the standard value and reference range of each lung function index; Step 5: Determine whether the theoretical values of all lung function indexes satisfy the reference range. If not, adjust the pressing force, and repeat Step 2 to Step 5 until the assisted breathing is completed.

2. The control method for the balloon ventilator presser according to claim 1, wherein The assisted breathing information includes the purpose of assisted breathing and the mode of assisted breathing.

3. The control method for a balloon ventilator presser according to claim 1, wherein Collect the respiratory rhythm parameters according to the first preset period. The respiratory rhythm parameters include the inspiratory start time. The calculation method of the respiratory frequency is: Step 31: After the start of any collection period, collect the inspiratory start time of the user in real time, and calculate the first respiratory frequency of the user based on the inspiratory start time; Step 32: Calculate the frequency fluctuation value of any two adjacent respiratory cycles based on the first respiratory frequency; Step 33: Determine whether there are N1 consecutive frequency fluctuation values that are less than or equal to the fluctuation threshold. If so, go to Step 34; if not, go to Step 35; Step 34: Take the average value of the N1 respiratory frequencies as the user's respiratory frequency, and then determine whether the user's respiratory frequency is between two respiratory grade ranges. If not, take the user's respiratory frequency as the respiratory frequency and end the collection of the respiratory rhythm parameters. If so, reduce the fluctuation threshold to generate a new fluctuation threshold, and then return to Step 33; Step 35: Take the average value of all the first respiratory frequencies within the first preset period as the respiratory frequency.

4. The control method for the balloon ventilator presser according to claim 3, characterized in that, The respiratory rhythm parameters include the expiratory start time. The calculation method of the inspiratory duration is: Obtain the expiratory start time of each respiratory cycle corresponding to the respiratory frequency; Calculate the difference between the expiratory start time and the inspiratory start time of any respiratory cycle, and define it as the first inspiratory duration of any respiratory cycle; Take the average value of the first inspiratory durations of all respiratory cycles corresponding to the respiratory frequency as the inspiratory duration.

5. The control method for a balloon ventilator presser according to claim 1, wherein The lung function indexes include lung elastic expansion ability and end-inspiratory stable pressure. Step 5 includes: Step 51: Determine whether the theoretical value of the lung elastic expansion ability is less than the reference range corresponding to the lung elastic expansion ability. If so, divide the pressing duration into a first pressing duration stage and a second pressing duration stage; Step 52: Obtain the standard value corresponding to the end-inspiratory stable pressure, define it as the first standard value, and set a first pressure greater than the first standard value based on the first standard value. Step 53: Increase the pressing force during the first pressing duration stage so that the airway pressure at the beginning of inspiration reaches the first pressure. During the second pressing duration stage, decrease the pressing force so that the end-inspiratory stable pressure is maintained at the first standard value.

6. The control method for a balloon ventilator presser according to claim 5, wherein, The lung function indicators include the amount of gas entering the airway per unit time and the inspiratory volume during the inspiratory duration. After step 53, it includes: Obtain the first inspiratory volume at the end of the second pressing duration stage and the first amount of gas entering the airway per unit time. When the first amount of gas entering the airway per unit time exceeds the preset range or the first inspiratory volume is lower than the reference range corresponding to the inspiratory volume, increase the first pressure, the first pressing duration stage, or the first standard value. When the first inspiratory volume is higher than the reference range corresponding to the inspiratory volume, decrease the first pressure, the first pressing duration stage, or the first standard value.

7. The control method for the balloon ventilator presser according to claim 5, characterized in that, The first pressure is a preset multiple of the first standard value, and the preset multiple is a positive number greater than 1 and less than 2.

8. The control method for the balloon ventilator presser according to claim 1, wherein Introduce a force feedback mechanism, including: Install a ceramic thick film sensor at the contact part between the presser and the balloon to real-time monitor the actual pressure value. When there is a difference between the actual pressure value and the pressing force, input the actual pressure value into the PID controller. The PID controller calculates a control signal based on the actual pressure value and the pressing force, and outputs the control signal to the actuator to adjust the output force of the presser so that the output force is maintained at the pressing force.

9. A control system for a balloon ventilator presser, characterized in that, The system includes: an initial setting module, a data acquisition module, a frequency adjustment module, a standard calculation module, and a pressure adjustment module. The initial setting module is used to obtain the user's basic information and assisted breathing information, and set the initial pressing parameters of the presser based on the basic information and the assisted breathing information. Among them, the pressing parameters include pressing force, pressing frequency, and pressing duration. The data acquisition module is used to collect the feedback information of assisted breathing, and the feedback information includes respiratory rhythm parameters and ventilation status parameters. The frequency adjustment module is used to calculate the user's inspiratory duration and respiratory frequency according to the respiratory rhythm parameters, and then adjust the pressing duration based on the inspiratory duration and adjust the pressing frequency based on the respiratory frequency. The standard calculation module is used to calculate the theoretical value of each lung function indicator according to the feedback information. At the same time, input the basic information and the feedback information into a preset model to obtain the standard value and reference range of each lung function indicator. The pressure adjustment module is used to determine whether the theoretical values of all lung function indicators meet the reference range. If not, adjust the pressing force.

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