Pressure compensation control method, device and equipment for breathing equipment and medium

Abstract

The invention discloses a pressure compensation control method and device for breathing equipment, the equipment and a medium. The method comprises the steps that the tidal volume of a user using the breathing equipment and the gas flow rate of breathing gas at the current moment are obtained; setting a tidal volume weight parameter for controlling the tidal volume at the next moment and a gas flow rate weight parameter for controlling the gas flow rate at the next moment; obtaining the tidal volume compensation amount of the next moment according to the product of the tidal volume weight parameter and the tidal volume; according to the product of the gas flow rate weight parameter and the gas flow rate, obtaining the gas flow rate compensation amount of the next moment; according to the sum of the tidal volume compensation amount and the gas flow rate compensation amount, the airway pressure compensation amount at the next moment is obtained; and performing pressure compensation on the output pressure value of the breathing equipment at the next moment according to the obtained output pressure value and the airway pressure compensation amount at the current moment. The problem that constant pressure support provided by a ventilation mode of existing breathing equipment is prone to causing insufficient ventilation support or excessive ventilation support is solved.

Description

Technical Field

[0001] The present invention relates to the field of automatic control, and in particular to a pressure compensation control method, device, equipment and medium for respiratory equipment. Background Art

[0002] Respiratory equipment refers to devices that can assist or replace the human respiratory function, mainly including medical devices such as ventilators and anesthesia machines. Respiratory equipment plays a vital role in modern medicine. They can assist or replace the human respiratory function and provide users with necessary respiratory support. These devices play an important role in medical first aid, home care and other fields.

[0003] The ventilation modes commonly used in current respiratory equipment still have some shortcomings in correcting the physiological relationship between the patient's inspiratory force and ventilation effect. The size of the inspiratory resistance of the respiratory muscles changes continuously with the contraction and expansion of the lungs and the inspiratory flow rate. The size of the inspiratory and expiratory force of the respiratory muscles has no effect on the pressure support set by the ventilator, but the pressure support provided by the existing ventilator is constant, resulting in insufficient or excessive ventilation support, leading to human-machine confrontation, thereby causing lung damage to the patient. Summary of the invention

[0004] The embodiments of the present invention provide a pressure compensation control method, device, equipment and medium for a respiratory device to solve the problem that the constant pressure support provided by the ventilation mode of the existing respiratory device easily causes insufficient ventilation support or excessive ventilation support.

[0005] In a first aspect, a pressure compensation control method for a respiratory device is provided, comprising: Obtaining the tidal volume and gas flow rate of the breathing gas of the user of the breathing device at the current moment; Setting a tidal volume weight parameter for controlling the tidal volume at a next moment, and a gas flow rate weight parameter for controlling the gas flow rate at a next moment; According to the product of the tidal volume weight parameter and the tidal volume, the tidal volume compensation amount at the next moment is obtained; according to the product of the gas flow rate weight parameter and the gas flow rate, the gas flow rate compensation amount at the next moment is obtained; according to the sum of the tidal volume compensation amount and the gas flow rate compensation amount, the airway pressure compensation amount at the next moment is obtained; The output pressure value of the respiratory device is obtained, and pressure compensation is performed on the output pressure value of the respiratory device at the next moment according to the output pressure value and the airway pressure compensation amount at the current moment.

[0006] In a second aspect, a pressure compensation control device for a respiratory device is provided, comprising: An acquisition module, used to acquire the tidal volume and gas flow rate of the breathing gas of the user of the breathing device at the current moment; A weight module, used for setting a tidal volume weight parameter for controlling the tidal volume at a next moment, and a gas flow rate weight parameter for controlling the gas flow rate at a next moment; A compensation module, configured to obtain a tidal volume compensation amount at a next moment according to the product of the tidal volume weight parameter and the tidal volume; obtain a gas flow rate compensation amount at a next moment according to the product of the gas flow rate weight parameter and the gas flow rate; and obtain an airway pressure compensation amount at a next moment according to the sum of the tidal volume compensation amount and the gas flow rate compensation amount; The output module is used to obtain the output pressure value of the respiratory device, and perform pressure compensation on the output pressure value of the respiratory device at the next moment according to the output pressure value and the airway pressure compensation amount at the current moment.

[0007] In a third aspect, a respiratory device is provided, comprising a memory, a processor, and a machine program stored in the memory and executable on the processor, wherein the processor implements the steps of the pressure compensation control method of the above-mentioned respiratory device when executing the machine program.

[0008] In a fourth aspect, a readable storage medium is provided, wherein the readable storage medium stores a machine program, and when the machine program is executed by a processor, the steps of the pressure compensation control method of the above-mentioned respiratory device are implemented.

[0009] The above-mentioned pressure compensation control method, device, equipment and medium of a respiratory device have the following beneficial effects: The present invention includes obtaining a tidal volume compensation amount at the next moment according to the product of a set tidal volume weight parameter and the tidal volume; obtaining a gas flow rate compensation amount at the next moment according to the product of a set gas flow rate weight parameter and the gas flow rate; obtaining an airway pressure compensation amount at the next moment according to the sum of the tidal volume compensation amount and the gas flow rate compensation amount; and performing pressure compensation on the output pressure value of the respiratory device at the next moment according to the output pressure value of the respiratory device and the airway pressure compensation amount at the current moment.

[0010] The present invention assigns a tidal volume weight parameter to the tidal volume, assigns a gas flow rate weight parameter to the gas flow rate, and performs real-time dynamic adjustment of the compensation amount of the tidal volume and the gas flow rate respectively according to the set tidal volume weight parameter and the gas flow rate weight parameter, and realizes pressure compensation of the output pressure value of the respiratory device according to the compensation amount of the dynamically adjusted tidal volume and gas flow rate, thereby improving or solving the human-machine confrontation, as well as the phenomenon of insufficient or excessive ventilation, thereby improving the quality of mechanical ventilation. Therefore, the present invention solves the problem that the constant pressure support provided by the ventilation mode of the existing respiratory device is easy to cause insufficient or excessive ventilation support, thereby causing lung damage to the patient. BRIEF DESCRIPTION OF THE DRAWINGS

[0011] In order to more clearly illustrate the technical solutions of the embodiments of the present invention, the accompanying drawings required for use in the description of the embodiments of the present invention will be briefly introduced below. Obviously, the accompanying drawings in the following description are only some embodiments of the present invention. For ordinary technicians in this field, other accompanying drawings can be obtained based on these accompanying drawings without paying creative labor.

[0012] Figure 1 is a schematic diagram of an application environment of a pressure compensation control method for a respiratory device in one embodiment of the present invention; Figure 2 is a flow chart of a pressure compensation control method for a respiratory device according to an embodiment of the present invention; Figure 3 is a schematic diagram of a pressure compensation control device of a respiratory device according to an embodiment of the present invention; Figure 4 Schematic diagram of a breathing apparatus according to an embodiment of the present invention. DETAILED DESCRIPTION

[0013] The following will be combined with the drawings in the embodiments of the present invention to clearly and completely describe the technical solutions in the embodiments of the present invention. Obviously, the described embodiments are part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without creative work are within the scope of protection of the present invention.

[0014] The pressure compensation control method of the respiratory device provided by the embodiment of the present invention can be applied as follows: Figure 1 Specifically, the pressure compensation control method of the respiratory device is applied in a pressure compensation control system of the respiratory device, and the pressure compensation control system of the respiratory device includes: Figure 1 The client and server shown in the figure communicate with each other through the network to solve the problem that the constant pressure support provided by the ventilation mode of the existing respiratory equipment is easy to cause insufficient or excessive ventilation support, thereby causing lung damage to the user. Among them, the client, also known as the user end, refers to a program corresponding to the server that provides local services to the client. The client can be installed on but not limited to various personal computers, laptops, smart phones, tablets and portable wearable devices. The server can be implemented as an independent server or a server cluster consisting of multiple servers.

[0015] In one embodiment, if Figure 2 A pressure compensation control method for a respiratory device disclosed in an embodiment of the present invention includes the following steps: S01: Acquire the tidal volume and gas flow rate of the breathing gas of the user of the breathing device at the current moment.

[0016] In this embodiment, tidal volume ‌ refers to the amount of gas inhaled or exhaled during each breath, usually expressed in milliliters. Tidal volume is the amount of gas delivered to the user's lungs each time during mechanical ventilation, and it is affected by many factors, including age, gender, volume surface, breathing habits, and body metabolism. It is the basis for evaluating lung function and ventilation efficiency. In natural breathing or mechanical ventilation, tidal volume is usually measured by changes in lung capacity and pressure.

[0017] In this embodiment, a flow sensor is used to detect the user's tidal volume. The flow sensor plays a vital role in the respiratory device. It is responsible for converting the inhaled and exhaled gas flow into electrical signals for subsequent signal processing and display. Depending on the function and design of the respiratory device, the flow sensor may be of different types, such as hot wire type, crystal hot film type, ultrasonic type, pressure sensing type and pressure differential type. Install the flow sensor in the air path system of the respiratory device to ensure that the sensor can accurately measure the gas flow. Usually the sensor is installed at the front end of the inhalation system or the end of the exhalation system.

[0018] When choosing the type of flow sensor, you can choose a suitable flow sensor according to the type of respiratory equipment and the specific situation of the user. Properly install the flow sensor in the air path system of the respiratory equipment to ensure that the flow sensor can accurately measure the flow of the gas. When the user breathes, the gas passes through the flow sensor, and the sensor converts the gas flow into electrical signals. These electrical signals are processed by the signal processing circuit and converted into digital signals for subsequent calculation and analysis.

[0019] Specifically, in this embodiment, the flow sensor performs real-time sampling (generally, once every 8ms for a ventilator), and the collected flow signal is integrated within a complete breathing cycle (including the inhalation phase and the exhalation phase) to obtain the total amount of gas inhaled or exhaled, that is, the tidal volume. The specific calculation method may involve real-time compensation of the flow signal to eliminate the influence of interference factors such as pressure and temperature on the measurement results. The calculated tidal volume is generally displayed on the display screen of the respiratory device for the user to view.

[0020] In this embodiment, the same flow sensor is used to collect the gas flow rate of the user's breathing gas. The flow sensor detects the flow rate of the breathing gas in real time and converts it into an electrical signal. After these electrical signals are processed by the signal processing circuit, the flow rate value can be displayed in real time on the display screen of the respiratory device. S02: setting a tidal volume weight parameter for controlling the tidal volume at a next moment, and a gas flow rate weight parameter for controlling the gas flow rate at a next moment.

[0021] Specifically, this embodiment controls and balances the compensation of the tidal volume to the output pressure value of the respiratory device by assigning a tidal volume weight parameter to the tidal volume; similarly, controls and balances the compensation of the gas flow rate to the output pressure value of the respiratory device by assigning a gas flow rate weight parameter to the gas flow rate. When the gas flow rate and tidal volume of the user's breathing gas need to be assisted, the weight parameter can be used to control a pressure support proportional to the inspiratory force, which is equivalent to amplifying the user's instantaneous inspiratory force, so that the respiratory device provides synchronous pressure support according to the amplified instantaneous inspiratory force, thereby improving or resolving the human-machine confrontation and the phenomenon of insufficient or excessive ventilation, thereby improving the quality of mechanical ventilation.

[0022] S03: According to the product of the tidal volume weight parameter and the tidal volume, the tidal volume compensation amount at the next moment is obtained; according to the product of the gas flow rate weight parameter and the gas flow rate, the gas flow rate compensation amount at the next moment is obtained; according to the sum of the tidal volume compensation amount and the gas flow rate compensation amount, the airway pressure compensation amount at the next moment is obtained.

[0023] Considering that the ventilation mechanism of the lungs is the result of the combined effect of the power and resistance of gas flow. The inspiratory power comes from the contraction of inspiratory muscles such as the diaphragm, and the resistance includes airway resistance Rr and elastic resistance Re. The pressure to overcome the airway resistance Rr during inhalation is proportional to the gas flow rate Ft, and the pressure to overcome the elastic resistance Re of the lungs during inhalation is proportional to the tidal volume Vt. Secondly, pressure support is equal to amplifying the user's instantaneous inspiratory force. Through real-time sampling by the flow sensor of the respiratory equipment (generally once every 8ms for a ventilator), when the user's inspiratory flow rate and tidal volume need assistance, providing a pressure support proportional to the intrathoracic pressure Pm generated by the contraction of the respiratory muscles is equal to amplifying the user's instantaneous inspiratory force, which is the dynamic pressure that needs to be compensated, thereby achieving dynamic compensation.

[0024] The pressure at which the user's inspiratory muscle force overcomes airway resistance (Rr) The calculation formula is: in, To overcome the airway resistance Rr, Rr is the airway resistance, is the gas flow rate, and the unit of Rr is cmH2O / L / s.

[0025] The pressure that the user needs to overcome the elastic resistance Re of the lungs when breathing with a breathing device The calculation formula is: in, To overcome the elastic resistance of the lungs, is the tidal volume, is elastic resistance, C is compliance, and Re is in cmH2O / L. Therefore, the pressure that needs to be applied at the moment of breathing is: (1) in, The pressure required for breathing. To overcome the pressure of airway resistance Rr, To overcome the elastic resistance of the lungs, is the gas flow rate, Rr is the airway resistance, is the tidal volume, According to the respiratory mechanics settings, Rr and Re are the user's current airway resistance and elastic resistance (elastic resistance = 1 / compliance), respectively. Airway resistance and compliance can be measured by the machine.

[0026] When the user breathes spontaneously, the only pressure provided is the pressure Pm generated by the respiratory muscles, so the pressure that needs to be applied at the moment of breathing is: (2) in, is the pressure required to be applied at the moment of breathing, Pm is the pressure generated by the respiratory muscles, is the gas flow rate, Rr is the airway resistance, is the tidal volume, It is elastic resistance.

[0027] When the respiratory device provides respiratory support, the pressure that needs to be applied at the moment of breathing is Pa, which is composed of the respiratory muscle pressure Pm and the airway pressure Paw generated by the respiratory device. Therefore, the pressure that needs to be applied at the moment of breathing is: (3) in, is the pressure required to be applied at the moment of breathing, Pm is the pressure generated by the respiratory muscles, The airway pressure generated by the breathing device, is the gas flow rate, Rr is the airway resistance, is the tidal volume, It is elastic resistance.

[0028] According to formula (3), the pressure generated by the respiratory muscles is: (4) Where Pm is the pressure generated by the respiratory muscles, The pressure required for breathing. It is the airway pressure generated by the respiratory device. Since Paw is proportional to the gas flow rate and tidal volume, the specific calculation formula of Paw is: (5) in, The airway pressure generated by the breathing device, is the gas flow rate, is the tidal volume, K1 is the ratio of Paw to tidal volume Vt, and K2 is the ratio of Paw to inspiratory flow rate Ft.

[0029] Will and Substituting the calculation formulas (1) and (5) into formula (4), the relevant calculation formula for Pm can be obtained as follows: (6) in, is the pressure required to be applied at the moment of breathing, Pm is the pressure generated by the respiratory muscles, The airway pressure generated by the breathing device, is the gas flow rate, Rr is the airway resistance, is the tidal volume, is the elastic resistance, K1 is the ratio of Paw to tidal volume Vt, and its unit is the same as the elastic resistance, cmH2O / L; K2 is the ratio of Paw to inspiratory flow rate Ft, and its unit is the same as the viscous resistance, cmH2O / L / s.

[0030] In order to improve or resolve the human-machine confrontation, it is necessary to make Pm=0 as much as possible, so the airway pressure Paw generated by the respiratory device is: (7) in, The airway pressure generated by the breathing device, is the gas flow rate, Rr is the airway resistance, is the tidal volume, is elastic resistance, C is compliance, is the gas flow rate auxiliary pressure, is the tidal volume assist pressure.

[0031] In this embodiment, the flow sensor measures Vt and Ft at the current sampling time, and performs compensation in the next flow sensor sampling interval. A breathing cycle of the breathing device is divided into t 0 , t 1 , ..., t n ; Currently, the gas flow rate and tidal volume detected by the flow sensor in any time period t are Ft n and Vt n , when Pm=0, the following calculation formula is obtained according to formula (6): (8) in, The airway pressure generated by the breathing device, is the gas flow rate at the current sampling moment, Rr is the airway resistance, is the tidal volume at the current sampling moment, C is compliance, K1 is the ratio of Paw to tidal volume Vt, and K2 is the ratio of Paw to inspiratory flow rate Ft, and the units are cmH2O / L / s respectively.

[0032] Therefore, according to the above formula (8), when the user's inspiratory flow rate and tidal volume need to be assisted, a suitable setting value can be given to K1 and K2 to provide the user with a pressure support proportional to the intrathoracic pressure Pm generated by the contraction of the respiratory muscles. This pressure support is the dynamic pressure that the user needs to compensate. Specifically, the tidal volume (i.e., ) and the tidal volume weight parameter (i.e. K2) obtained in step S02, the tidal volume compensation required for the output pressure value of the respiratory device at the next moment can be obtained; the gas flow rate (i.e. ) and the gas flow rate weight parameter (i.e. K1) obtained in step S02 are also multiplied together to obtain the gas flow rate compensation required for the output pressure value of the respiratory device at the next moment; the tidal volume compensation amount is added to the gas flow rate compensation amount to obtain the airway pressure compensation required for the output pressure value of the respiratory device at the next moment. The specific calculation formula is as follows: in, is the airway pressure compensation, is the gas velocity weight parameter, is the sampled value of the gas flow rate, is the tidal volume weight parameter, is the sampled value of tidal volume.

[0033] S04: Obtaining the output pressure value of the respiratory device, and performing pressure compensation on the output pressure value of the respiratory device at a next moment according to the output pressure value and the airway pressure compensation amount at a current moment.

[0034] Specifically, when dynamic pressure compensation is turned on, at every moment of inhalation, the airway pressure generated by the respiratory device increases as the inspiratory muscle strength increases. At this time, the inspiratory force of the respiratory muscles is compensated according to the set airway pressure. Enhancement is to add an airway pressure compensation value based on the airway pressure value provided by the original respiratory device. The pressure value of the breathing device is used to compensate the output pressure value of the breathing device at the next moment; when the inspiratory muscle strength weakens, the airway pressure also decreases, that is, the airway pressure compensation value is subtracted from the airway pressure value provided by the original breathing device. The pressure value of the breathing device is adjusted to the output pressure value of the breathing device at the next moment; when the breathing device detects that the inspiratory muscle force plus the airway pressure is lower than the elastic retraction pressure of the respiratory system, the inhalation stops and the exhalation starts, and the exhalation completes a breathing cycle. Pressure compensation is repeated in this way to assist ventilation. Through airway pressure assistance, the user controls the breathing form of each breathing cycle, and the inspiratory muscle force determines the start, maintenance and termination of the ventilator's air supply. Spontaneous breathing and ventilator air supply phases can maintain good synchronization. Users can adjust the breathing form according to their own different ventilation needs.

[0035] Dynamic pressure compensation is a form of assisted ventilation, which requires the user to breathe normally and spontaneously. According to the above principle and method, if the user has no spontaneous breathing, there is no dynamic pressure compensation auxiliary function, and there is no need to set the tidal volume and respiratory rate. Therefore, when users with unstable spontaneous breathing use dynamic pressure compensation as an auxiliary ventilation function, they should set apnea ventilation as a standby, and set an apnea alarm to ensure the safety of using the dynamic pressure compensation auxiliary function; in addition, in clinical practice, when the user's breathing work is unstable or the breathing circuit vibrates, it is very easy to falsely trigger ventilation when using high auxiliary ratios K1 and K2 values, so the values ​​of K1 and K2 should not be too high.

[0036] The following are examples of specific parameter settings for regulating breathing forms in several special situations: For users with chronic obstructive pulmonary disease (COPD), increased airway resistance and increased functional residual gas lead to airway closure, and gas blockage produces intrinsic positive end-expiratory pressure (PEEPi). The inspiratory muscles must first overcome the intrinsic positive end-expiratory pressure to open the closed airway before inspiratory airflow can be generated. In the initial and final stages of inhalation, the inspiratory pressure changes significantly while the lung volume only increases slightly. During dynamic pressure compensation assistance, if the positive end-expiratory pressure (PEEP) is not set at the same time, the respiratory muscle force Pm must first overcome the intrinsic positive end-expiratory pressure to trigger ventilation. The intrinsic positive end-expiratory pressure weakens the ventilation assistance to varying degrees. Therefore, when dynamic pressure compensation assistance is used for COPD, the set positive end-expiratory pressure must be used first to expand the closed airway. The generally set positive end-expiratory pressure is generally 80% of the endogenous positive end-expiratory pressure, and then the above-mentioned dynamic pressure compensation assistance method is used to compensate and adjust the airway pressure. For users of Acute Respiratory Distress Syndrome (ARDS), the alveoli collapse in large quantities and the lung compliance is significantly reduced. If the positive end-expiratory pressure is not set, it will make it difficult for the alveoli to expand in the early stage of inspiration, which will also weaken the ventilation assistance effect. Therefore, when ARDS users apply dynamic pressure compensation assistance, they must also use the set positive end-expiratory pressure first. For example, during the inhalation stage, when the compliance C is detected to reach 50ml / mbar, the airway pressure sensor reads the airway pressure at this time, and then slowly increases the airway pressure compensation by 2 to 3 cmH2O based on this airway pressure.

[0037] The main purpose of the present invention is to provide a pressure compensation amount proportional to the inspiratory force when the user's inspiratory flow rate and tidal volume need assistance, which is equivalent to amplifying the user's instantaneous inspiratory force. An airway pressure compensation amount is obtained based on the set weight parameters and the user's instantaneous inspiratory force. , allowing respiratory equipment to provide users with synchronized pressure support, thereby improving or resolving human-machine conflict, as well as insufficient or excessive ventilation, and thereby improving the quality of mechanical ventilation.

[0038] In one embodiment, in the above step S02, that is, setting a tidal volume weight parameter for controlling the tidal volume at the next moment, and a gas flow rate weight parameter for controlling the gas flow rate at the next moment, comprises the following steps: S201: Obtain the airway resistance and elastic resistance of the user of the respiratory device at the current moment.

[0039] The airway resistance in this embodiment refers to the resistance generated when the gas flows through the respiratory tract, which is the pressure difference generated by the unit flow rate. It reflects the degree of obstruction encountered by the gas when it flows in the respiratory tract. The following are several commonly used airway resistance measurement methods: 1) The occlusion method is a simple and commonly used method for measuring airway resistance. The key is to ensure that the respiratory muscles are relaxed and the alveolar pressure is balanced with the airway opening pressure. By quickly blocking the respiratory passage and recording the flow rate before occlusion and the pressure after occlusion, the airway resistance can be calculated. The main advantage of this method is that it is simple and convenient to measure, and can be used for both routine measurement and clinical monitoring.

[0040] 2) Mechanical ventilation measurement is a method to directly measure airway resistance during mechanical ventilation. Its basic principle is to calculate airway resistance by measuring airway peak pressure and airflow velocity according to the fluid mechanics formula. The specific formula is: airway resistance = airway peak pressure / airflow velocity. This method can monitor the changes in airway resistance in real time and continuously, which is of great significance for evaluating respiratory system function and guiding mechanical ventilation treatment.

[0041] 3) Esophageal manometry is a method of indirectly measuring airway resistance by placing a pressure measuring catheter in the esophagus. This method can measure the intraesophageal pressure at the starting point of inspiratory flow, which is equivalent to the pressure at the end of exhalation, namely PEEPi (intrinsic positive end-expiratory pressure). Although esophageal manometry is not a direct measure of airway resistance, it can provide pressure information related to airway resistance and help evaluate the functional status of the respiratory system.

[0042] The elastic resistance in this embodiment refers to the elastic resistance when the alveoli expand, including the elastic retraction force and surface tension of the alveoli. It is the resistance of inhalation and the driving force of exhalation. The measurement methods of lung elastic resistance usually include the following: 1) Direct measurement is to calculate lung elastic resistance by measuring changes in lung volume and transpulmonary pressure. This method requires professional equipment and operation techniques.

[0043] 2) Indirect measurement is to indirectly estimate lung elastic resistance by measuring the compliance of the respiratory system. Compliance is the ability of the respiratory system to respond to pressure changes and is inversely proportional to elastic resistance. Therefore, the size of lung elastic resistance can be indirectly assessed by measuring compliance.

[0044] This embodiment measures the airway resistance Rr by the above-mentioned mechanical ventilation measurement method. First, during the mechanical ventilation process, the monitoring function on the respiratory device is used to record the inspiratory peak pressure Ppeak and plateau pressure Pplat of the current respiratory device user and the corresponding inspiratory flow Flow. The inspiratory peak pressure is the highest pressure during the ventilator's air delivery process, the plateau pressure is the airway pressure at the end of the inspiratory breath hold (the inspiratory and expiratory valves are closed, and the airflow is zero), and the inspiratory flow is the flow rate of the gas flowing through the respiratory tract. Then, the airway resistance is calculated based on the measured inspiratory peak pressure Ppeak and plateau pressure Pplat and the corresponding inspiratory flow Flow, and the relevant calculation formula for the airway resistance Rr is: in, is airway resistance, Ppeak is peak inspiratory pressure, and Pplat is platform pressure. is the inspiratory flow.

[0045] This embodiment uses the above-mentioned indirect measurement method to calculate the lung elastic resistance. First, during mechanical ventilation, the monitoring function on the respiratory device is used to record the plateau pressure Pplat at the end of inspiration and the pressure PEEP at the end of expiration. The plateau pressure is the value when the pressure in the airway is stable at the end of the inspiratory phase, which reflects the pressure in the alveoli. The end-expiratory pressure is the residual pressure in the airway at the end of the expiratory phase. Then, the compliance is calculated based on the measured tidal volume Vt, the inspiratory plateau pressure Pplat, and the end-expiratory pressure PEEP. The relevant calculation formula for the compliance C of the respiratory system is: in, is compliance, Vt is the measured tidal volume, Pplat is the plateau pressure, is the end-expiratory pressure. Finally, the elastic resistance is calculated based on the compliance C. The relevant calculation formula for the elastic resistance Re is: Among them, Re is the elastic resistance and C is the compliance.

[0046] S202: Obtain a tidal volume weight parameter according to the airway resistance and a preset airway resistance threshold, and obtain a gas flow rate weight parameter according to the elastic resistance and a preset elastic resistance threshold.

[0047] Specifically, the tidal volume weight parameter is calculated based on the airway resistance obtained in step S01 and a preset airway resistance threshold. Calculating the tidal volume weight parameter may include: In this embodiment, the airway resistance threshold is set according to the normal value of airway resistance. The normal value range of airway resistance varies due to individual differences, age, gender, height, weight, and measurement methods. In general, the normal value of airway resistance is generally considered to be relatively low to ensure smooth breathing. However, there is no absolute uniform standard for the specific normal value range. Some literature and research may give specific ranges, but these ranges may vary due to different measurement methods, instruments, and populations.

[0048] For adults, the normal range of airway resistance is roughly between 1 and 3 cmH2O / (L / s), but this may vary from study to study. The normal range of airway resistance for children may change with age and is usually slightly higher than that for adults.

[0049] Therefore, when setting the airway resistance threshold, multiple attempts can be made based on the user's own specific situation to ensure that the user's breathing is smooth.

[0050] The gas flow rate weight parameter is calculated based on the elastic resistance obtained in the above step S01 and the preset elastic resistance threshold. Calculating the gas flow rate weight parameter may include: In this embodiment, the airway resistance threshold is set according to the normal value of elastic resistance. However, the elastic resistance of the lung can be expressed by lung compliance, that is, the ratio of the change in lung volume to the change in transpulmonary pressure. The compliance of a normal adult lung is about 2.0L / kPa (or 0.2L / cmH2O), which means that when the transpulmonary pressure changes by 1kPa (or 1cmH2O), the lung volume can change by 2.0L (or 0.2L). The compliance of the lung is inversely proportional to the elastic resistance, that is, the greater the compliance, the smaller the elastic resistance; conversely, the smaller the compliance, the greater the elastic resistance. However, when setting the elastic resistance threshold, you can try to set it multiple times according to the user's own specific situation to ensure that the user breathes smoothly.

[0051] The pressure compensation control method of the respiratory device of this embodiment, when setting the tidal volume weight parameter and the gas flow rate weight parameter by using airway resistance and elastic resistance, takes into account that lung ventilation includes the interaction of two factors, one is the power of inspiration, that is, the pressure of gas flow; the other is the resistance that prevents gas flow, that is, the resistance of inspiration. The power of inspiration comes from the contraction of inspiratory muscles such as the diaphragm, which reduces the intrathoracic pressure so that the intrapulmonary pressure is lower than the atmospheric pressure. This pressure difference allows gas to enter the lungs. Spontaneous breathing is caused by the periodic activation of the inspiratory muscles by the nerve center. The pressure generated by the contraction of the inspiratory muscles is affected by three factors: the size of the inspiratory muscle strength, the lung volume, and the inspiratory flow rate. During the inhalation process, the relationship between the inspiratory force and the pressure it generates is constantly changing. Respiratory resistance comes from airway viscous resistance and lung elastic resistance, and varies with total airway resistance. Airway viscous resistance (airway resistance is positively correlated with gas flow rate, while elastic resistance is positively correlated with lung volume. Therefore, the pressure required for intrathoracic pressure during inspiration is the sum of these two resistances. Since the pressure required for intrathoracic pressure during inspiration is closely related to the two resistances, when the present invention sets the tidal volume weight parameter and the gas flow rate weight parameter through airway resistance and elastic resistance, the calculation result of the airway pressure compensation amount can be made more accurate, so that the respiratory device can provide users with more accurate pressure support, further improving the quality of mechanical ventilation.

[0052] In one embodiment, the above step S202, i.e., obtaining the tidal volume weight parameter according to the airway resistance and the preset airway resistance threshold, includes the following steps: S301: Obtaining an airway resistance difference according to a difference between the airway resistance and a preset airway resistance threshold.

[0053] Specifically, the airway resistance of the user at the current moment obtained in the above step S202 is subtracted from the preset airway resistance threshold to obtain an airway resistance difference value, which is a measure of the difference between the actual airway resistance and the preset airway resistance threshold value. It can reflect in real time whether the user's airway resistance deviates from the preset standard. The airway resistance difference value in this embodiment is a scalar value, which is a quantity with only size but no direction.

[0054] S302: Obtaining the tidal volume weight parameter according to the ratio of the airway resistance difference to a preset airway resistance threshold.

[0055] Specifically, the ratio between the airway resistance difference obtained in step S301 and the preset airway resistance threshold is calculated to obtain the tidal volume weight parameter. The specific calculation formula is: in, is the tidal volume weight parameter, is the difference in airway resistance, is the preset airway resistance threshold, It is the user's current airway resistance.

[0056] The calculation process of the tidal volume weight parameter is further explained below through specific numerical values. Assuming that the airway resistance Rr increases from the normal value of 4 cmH2O / L / s to 7 cmH2O / L / s, the airway resistance difference for: Among them, the normal value of 4 cmH2O / L / s is the preset airway resistance threshold N1, and 7 cmH2O / L / s is the user's current airway resistance , this airway resistance difference indicates that the user's current airway resistance deviates from the preset airway resistance threshold of 3 cmH2O / L / s. Therefore, according to the above calculation results, K1 is set to 0.75 cmH2O / L / s.

[0057] The present invention calculates the change in airway resistance at the current moment relative to the preset airway resistance threshold, and then obtains the tidal volume weight parameter according to the ratio of the change to the preset airway resistance threshold. Since the pressure required for intrathoracic pressure during inspiration is closely related to airway resistance, the tidal volume is adaptively adjusted according to the real-time change of airway resistance to ensure the stability of ventilation efficiency. When airway resistance increases, by increasing the tidal volume weight parameter, the reduction in ventilation volume caused by the increase in resistance can be compensated, thereby maintaining adequate ventilation and further improving the quality of mechanical ventilation.

[0058] In one embodiment, the above step S03, i.e., obtaining the gas flow rate weight parameter according to the elastic resistance and the preset elastic resistance threshold, includes the following steps: S401: converting the elastic resistance into an elastic resistance compliance value, and converting the preset elastic resistance threshold into a preset elastic resistance compliance threshold.

[0059] In this embodiment, it is considered that the size of elastic resistance is affected by many factors. If a direct measurement method is used to directly measure the size of elastic resistance, it will be difficult and the measurement result will be inaccurate. Therefore, in this embodiment, elastic resistance is converted into lung compliance. Compliance is the ability of the respiratory system to respond to pressure changes and is inversely proportional to elastic resistance. Therefore, the change in the size of lung elastic resistance can be indirectly evaluated by measuring compliance. The specific conversion formula between elastic resistance and compliance is: Among them, Re is the elastic resistance and C is the compliance.

[0060] S402: Obtaining a compliance difference value according to a difference between the elastic resistance compliance value and the preset elastic resistance compliance threshold value.

[0061] The compliance difference is a measure of the difference between the actual elastic resistance compliance value and the standard preset elastic resistance compliance threshold. It can reflect in real time whether the user's compliance deviates from the preset standard. The compliance difference is obtained by subtracting the elastic resistance compliance value obtained in the above step S401 from the preset elastic resistance compliance threshold. The compliance difference in this embodiment is a scalar value, which is a quantity with only size but no direction.

[0062] S403: Obtaining the gas flow rate weight parameter according to the ratio of the compliance difference to a preset elastic resistance compliance threshold.

[0063] Specifically, the ratio between the compliance difference obtained in the above step S402 and the preset elastic resistance compliance threshold is calculated to obtain the gas flow rate weight parameter. The specific calculation formula is: in, is the compliance difference, is the elastic resistance compliance value of the user at the current moment, is the preset elastic resistance compliance threshold, 2 is the gas flow rate weight parameter.

[0064] The calculation process of the gas flow rate weight parameter is further explained below through specific numerical values. Assuming that the compliance is reduced from 100 ml / cmH2O to 29 ml / cmH2O, the compliance difference corresponding to the compliance is: Among them, 100 ml / cmH2O is the preset elastic resistance compliance threshold value N2, and this compliance difference value indicates that the elastic resistance compliance value at the current moment deviates from the preset elastic resistance compliance threshold value 71 mL / cmH2O. Therefore, K2 is set to 0.71 cmH2O / L / s.

[0065] The pressure compensation control method of the respiratory device of this embodiment converts the elastic resistance into a compliance value, obtains the compliance value according to the elastic resistance compliance value and the preset elastic resistance compliance threshold, and then obtains the gas flow rate weight parameter according to the ratio of the compliance difference value and the preset elastic resistance compliance threshold. Since the size of the elastic resistance is affected by many factors, it is difficult to directly measure the size of the elastic resistance using a direct measurement method, and the measurement result is also inaccurate. Therefore, this embodiment converts the elastic resistance into the compliance of the lung to calculate the gas flow rate weight parameter, which can make the calculation result of the weight parameter more accurate, and can more accurately control the gas flow rate, thereby maintaining adequate ventilation and further improving the quality of mechanical ventilation.

[0066] In one embodiment, in the above step S02, that is, setting a tidal volume weight parameter for controlling the tidal volume at the next moment, and a gas flow rate weight parameter for controlling the gas flow rate at the next moment, comprises the following steps: S501: Obtain the respiratory muscle pressure value of the user of the respiratory device at the current moment.

[0067] The respiratory muscle pressure in the present embodiment refers to the force generated by the respiratory muscles during the breathing process, and this force is the power source of the respiratory movement. The respiratory muscles include inspiratory muscles and expiratory muscles. The inspiratory muscles are mainly the diaphragm and the external intercostal muscles, which expand the thorax by contraction to produce the inhalation movement; the expiratory muscles are mainly the abdominal muscles and the internal intercostal muscles, which shrink the thorax by contraction to produce the exhalation movement. The size of the respiratory muscle pressure depends on the contraction strength and contraction speed of the respiratory muscles, and is also affected by factors such as the elasticity of the thorax and lung tissue, and airway resistance. When the respiratory muscles contract, they will generate a certain pressure, which is the power to push gas in and out of the lungs. Under normal circumstances, the respiratory muscle pressure is balanced with the intrapulmonary pressure, so that the respiratory movement can proceed smoothly.

[0068] However, in some cases, respiratory muscle pressure may change. For example, when suffering from respiratory diseases or neuromuscular diseases, respiratory muscles may be damaged, resulting in decreased respiratory muscle strength and reduced respiratory muscle pressure, thereby affecting respiratory function. Therefore, this embodiment controls the pressure value output by the compensating respiratory device by detecting changes in respiratory muscle pressure, thereby providing respiratory support for the user. Respiratory muscle stress can be measured in a variety of ways, usually including the following: Esophageal pressure measurement (Pes) is the gold standard for assessing respiratory muscle pressure. By inserting an esophageal pressure catheter into the esophagus, the pressure changes in the esophagus can be measured, thereby indirectly reflecting the pressure of the respiratory muscles (mainly the diaphragm). Esophageal pressure measurement can calculate the respiratory muscle pressure, which is the difference between the static rebound pressure of the chest wall and the total esophageal pressure. In addition, the esophageal pressure-time product is also an important indicator for assessing the energy consumption of the respiratory muscles.

[0069] Electrical Activity of the Diaphragm (EAdi) monitoring is to monitor the electrical activity of the diaphragm by setting electrodes in the esophagus. EAdi is closely related to diaphragm pressure and changes proportionally with the level of respiratory assistance. By monitoring Eadi, the user's respiratory drive and respiratory muscle effort can be assessed. In addition, the EAdi value can be converted to conventional respiratory muscle pressure by calculating neuromuscular efficiency (i.e., the ratio between the drop in airway pressure and EAdi).

[0070] This embodiment obtains the respiratory muscle pressure value of the respiratory device user at the current moment by using the esophageal pressure measurement method.

[0071] S502: Obtaining the tidal volume weight parameter and the gas flow rate weight parameter according to the respiratory muscle pressure value and the preset respiratory muscle pressure threshold, wherein the tidal volume weight parameter and the gas flow rate weight parameter are equal.

[0072] Specifically, this embodiment first calculates the difference between the respiratory muscle pressure value and the preset respiratory muscle pressure threshold to obtain a respiratory muscle pressure difference; and obtains the tidal volume weight parameter according to the ratio of the respiratory muscle pressure value difference to the preset elastic resistance threshold. The tidal volume weight parameter is set equal to the gas flow rate weight parameter. The specific calculation formula is: in, is the gas velocity weight parameter, is the tidal volume weight parameter, N3 is the preset respiratory muscle pressure threshold, It is the respiratory muscle pressure value of the user at the current moment.

[0073] If the pathophysiological changes lead to a decrease in Pm, so that the respiratory muscle function is only half of the normal capacity, then K1 and K2 should be set to: in, is the respiratory muscle pressure value of the user at the current moment, is the preset respiratory muscle pressure threshold. Therefore, K1 and K2 are set to 0.5 To calculate the corresponding , to compensate in equal proportion for the reduced respiratory muscle work caused by the disease.

[0074] The pressure compensation control method of the respiratory device of this embodiment obtains the tidal volume weight parameter and the gas flow rate weight parameter through the respiratory muscle pressure value and the preset respiratory muscle pressure threshold. Different users have different respiratory muscle strength and ventilation needs. By measuring the respiratory muscle pressure value and comparing it with the preset threshold, the tidal volume and gas flow rate parameters can be tailored for each user, thereby achieving more personalized treatment. Accurate parameter settings can ensure that the ventilation volume provided by the ventilator is neither too much nor too little, thereby avoiding the occurrence of ventilator-related complications such as barotrauma and volume trauma, and further improving the quality of mechanical ventilation.

[0075] In one embodiment, in the above step S02, that is, setting a tidal volume weight parameter for controlling the tidal volume at the next moment, and a gas flow rate weight parameter for controlling the gas flow rate at the next moment, comprises the following steps: S601: Obtain a pressure adjustment instruction issued by a user, and determine the tidal volume weight parameter and the gas flow rate weight parameter according to the pressure adjustment instruction, and the tidal volume weight parameter and the gas flow rate weight parameter are equal.

[0076] The pressure adjustment instructions in this embodiment refer to a series of operation instructions for adjusting and controlling the output pressure of the respiratory device, ensuring that the output pressure of the respiratory device is maintained within a predetermined range to meet the user's breathing needs.

[0077] In this embodiment, the user issues a pressure adjustment command through the interface or controller handle of the respiratory device. The user inputs the tidal volume weight parameter and gas flow rate weight parameter settings of the pressure compensation value to be set on the interface or controller handle of the respiratory device. After the control system of the respiratory device reads the tidal volume weight parameter and gas flow rate weight parameter settings set by the user, it uses the set values ​​of the tidal volume weight parameter and gas flow rate weight parameter read to calculate the airway pressure compensation value. .

[0078] Specifically, in the process of controlling the setting of the tidal volume weight parameter and the gas flow rate weight parameter, if the airway pressure value output by the respiratory device is too high, the value of the tidal volume weight parameter or the gas flow rate weight parameter can be reduced through the interface of the respiratory device or the controller handle to reduce the air supply volume and air supply speed, thereby reducing the airway pressure compensation amount and reducing the airway pressure. If the airway pressure value output by the respiratory device is too low, the value of the tidal volume weight parameter or the gas flow rate weight parameter can be increased through the interface of the respiratory device or the controller handle to increase the air supply volume and air supply speed, thereby increasing the airway pressure compensation amount and increasing the airway pressure. When adjusting the parameters, it is necessary to proceed step by step and closely observe the user's reaction and ventilation effect to ensure that the adjusted parameters can meet the user's ventilation needs.

[0079] The pressure compensation control method of the respiratory device of this embodiment determines the tidal volume weight parameter and the gas flow rate weight parameter through the pressure adjustment instruction. Through the pressure adjustment instruction, the user can fine-tune the ventilation support according to his or her own breathing feeling and needs by dynamically adjusting the weight parameters of the tidal volume and the gas flow rate, thereby enhancing the user's autonomy and comfort, thereby avoiding the occurrence of ventilator-related complications such as barotrauma and volutrauma, and further improving the quality of mechanical ventilation.

[0080] It should be understood that the order of execution of the steps in the above embodiment does not necessarily mean the order of execution. The execution order of each process should be determined by its function and internal logic, and should not constitute any limitation on the implementation process of the embodiment of the present invention.

[0081] In one embodiment, a pressure compensation control device for a respiratory device is provided, and the pressure compensation control device for the respiratory device corresponds one-to-one to the pressure compensation control method for the respiratory device in the above embodiment. Figure 3 As shown, the pressure compensation control device of the respiratory device includes an acquisition module, a weight module, a compensation module and an output module. The detailed description of each functional module is as follows: The acquisition module is used to acquire the tidal volume and gas flow rate of the breathing gas of the user of the breathing device at the current moment.

[0082] The weight module is used to set a tidal volume weight parameter for controlling the tidal volume at the next moment, and a gas flow rate weight parameter for controlling the gas flow rate at the next moment.

[0083] A compensation module is used to obtain a tidal volume compensation amount at a next moment according to the product of the tidal volume weight parameter and the tidal volume; to obtain a gas flow rate compensation amount at a next moment according to the product of the gas flow rate weight parameter and the gas flow rate; and to obtain an airway pressure compensation amount at a next moment according to the sum of the tidal volume compensation amount and the gas flow rate compensation amount.

[0084] The output module is used to obtain the output pressure value of the respiratory device, and perform pressure compensation on the output pressure value of the respiratory device at the next moment according to the output pressure value and the airway pressure compensation amount at the current moment.

[0085] The main purpose of the present invention is to provide a pressure compensation amount proportional to the inspiratory force when the user's inspiratory flow rate and tidal volume need assistance, which is equivalent to amplifying the user's instantaneous inspiratory force. An airway pressure compensation amount is obtained based on the set weight parameters and the user's instantaneous inspiratory force. , allowing respiratory equipment to provide users with synchronized pressure support, thereby improving or resolving human-machine conflict, as well as insufficient or excessive ventilation, and thereby improving the quality of mechanical ventilation.

[0086] The specific definition of the pressure compensation control device of the respiratory device can be found in the definition of the pressure compensation control method of the respiratory device above, which will not be repeated here. Each module in the pressure compensation control device of the above-mentioned respiratory device can be implemented in whole or in part by software, hardware and a combination thereof. The above-mentioned modules can be embedded in or independent of the processor in the machine device in the form of hardware, or can be stored in the memory of the machine device in the form of software, so that the processor can call and execute the operations corresponding to the above modules.

[0087] In one embodiment, Figure 4 This is a schematic diagram of the structure of a breathing device provided by Embodiment 4 of the present invention. Figure 4 As shown, the breathing device of this embodiment includes: at least one processor ( Figure 4 Only one is shown), a memory, and a machine program stored in the memory and executable on at least one processor, wherein when the processor executes the machine program, the steps of any of the above-mentioned pressure compensation control method embodiments of the respiratory device are implemented.

[0088] The breathing device may include, but is not limited to, a processor and a memory. A person skilled in the art will understand that Figure 4 This is merely an example of a respiratory device and does not constitute a limitation on the respiratory device. The respiratory device may include more or fewer components than shown in the figure, or a combination of certain components, or different components, for example, it may also include a network interface, a display screen, and an input device.

[0089] The processor may be a CPU, or other general-purpose processors, a digital signal processor (DSP), an application-specific integrated circuit (ASIC), a field-programmable gate array (FPGA) or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components, etc. A general-purpose processor may be a microprocessor or any conventional processor, etc.

[0090] The memory includes a readable storage medium, an internal memory, etc., wherein the internal memory may be the memory of the machine device, and the internal memory provides an environment for the operation of the operating system and the machine-readable instructions in the readable storage medium. The readable storage medium may be a hard disk of the machine device, and in other embodiments, it may also be an external storage device of the machine device, for example, a plug-in hard disk, a smart memory card (Smart Media Card, SMC), a secure digital (SecureDigital, SD) card, a flash card (Flash Card), etc. equipped on the machine device. Further, the memory may also include both an internal storage unit of the machine device and an external storage device. The memory is used to store an operating system, an application program, a boot loader (BootLoader), data, and other programs, such as the program code of the machine program, etc. The memory may also be used to temporarily store data that has been output or is to be output.

[0091] The technicians in the relevant field can clearly understand that for the convenience and simplicity of description, only the division of the above-mentioned functional units and modules is used as an example. In practical applications, the above-mentioned function allocation can be completed by different functional units and modules as needed, that is, the internal structure of the device is divided into different functional units or modules to complete all or part of the functions described above. The functional units and modules in the embodiment can be integrated into a processing unit, or each unit can exist physically separately, or two or more units can be integrated into one unit. The above-mentioned integrated unit can be implemented in the form of hardware or in the form of software functional units. In addition, the specific names of the functional units and modules are only for the convenience of distinguishing each other, and are not used to limit the scope of protection of the present invention. The specific working process of the units and modules in the above-mentioned device can refer to the corresponding process in the above-mentioned method embodiment, which will not be repeated here. If 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 machine-readable storage medium. Based on such understanding, the present invention implements all or part of the processes in the above-mentioned embodiment method, which can be completed by instructing the relevant hardware through a machine program, and the machine program can be stored in a machine-readable storage medium. When the machine program is executed by the processor, the steps of the above-mentioned method embodiment can be implemented. Among them, the machine program includes machine program code, and the machine program code can be in source code form, object code form, executable file or some intermediate form. The machine-readable medium may at least include: any entity or device capable of carrying machine program code, recording medium, machine memory, read-only memory (ROM), random access memory (RAM), electric carrier signal, telecommunication signal and software distribution medium. For example, a USB flash drive, a mobile hard disk, a magnetic disk or an optical disk. In some jurisdictions, according to legislation and patent practice, machine-readable media cannot be electric carrier signals and telecommunication signals.

[0092] The present invention implements all or part of the processes in the above-mentioned method embodiments, and may also be completed through a machine program product. When the machine program product runs on a respiratory device, the respiratory device can implement the steps in the above-mentioned method embodiments when executing the machine program product.

[0093] In the above embodiments, the description of each embodiment has its own emphasis. For parts that are not described or recorded in detail in a certain embodiment, reference can be made to the relevant descriptions of other embodiments.

[0094] In one embodiment, a machine-readable storage medium is provided, on which a machine program is stored. When the machine program is executed by a processor, the pressure compensation control method of the respiratory device in the above embodiment is implemented, for example Figure 2S01-S04 are shown, and will not be described here in detail to avoid repetition. Alternatively, when the machine program is executed by the processor, the functions of each module in the embodiment of the pressure compensation control device of the above-mentioned respiratory device are realized, for example Figure 3 The functions of the acquisition module, weight module, compensation module and output module shown are not repeated here to avoid repetition.

[0095] Those of ordinary skill in the art can understand that all or part of the processes in the above-mentioned embodiment methods can be implemented by instructing the relevant hardware through a machine program, and the machine program can be stored in a non-volatile machine-readable storage medium. When the machine program is executed, it can include the processes of the embodiments of the above-mentioned methods. Among them, any reference to memory, storage, database or other media used in the embodiments provided in this application may include non-volatile and / or volatile memory. Non-volatile memory may include read-only memory (ROM), programmable ROM (PROM), electrically programmable ROM (EPROM), electrically erasable programmable ROM (EEPROM) or flash memory. Volatile memory may include random access memory (RAM) or external cache memory. By way of illustration and not limitation, RAM is available in many forms, such as static RAM (SRAM), dynamic RAM (DRAM), synchronous DRAM (SDRAM), double data rate SDRAM (DDRSDRAM), enhanced SDRAM (ESDRAM), synchronous link (Synchlink) DRAM (SLDRAM), memory bus (Rambus) direct RAM (RDRAM), direct memory bus dynamic RAM (DRDRAM), and memory bus dynamic RAM (RDRAM), etc.

[0096] The present invention implements all or part of the processes in the above-mentioned method embodiments, and may also be completed through a machine program product. When the machine program product runs on a respiratory device, the respiratory device can implement the steps in the above-mentioned method embodiments when executing the machine program product.

[0097] In the above embodiments, the description of each embodiment has its own emphasis. For parts that are not described or recorded in detail in a certain embodiment, reference can be made to the relevant descriptions of other embodiments.

[0098] Those skilled in the art will appreciate that the units and algorithm steps of each example described in conjunction with the embodiments disclosed herein can be implemented in electronic hardware, or a combination of computer software and electronic hardware. Whether these functions are performed in hardware or software depends on the specific application and design constraints of the technical solution. Professional and technical personnel can use different methods to implement the described functions for each specific application, but such implementation should not be considered to be beyond the scope of the present invention.

[0099] In the embodiments provided by the present invention, it should be understood that the disclosed devices / respiratory equipment and methods can be implemented in other ways. For example, the device / respiratory equipment embodiments described above are only schematic. For example, the division of modules or units is only a logical function division. There may be other division methods in actual implementation. For example, multiple units or components can be combined or integrated into another system, or some features can be ignored or not executed. Another point is that the mutual coupling or direct coupling or communication connection shown or discussed can be through some interfaces, indirect coupling or communication connection of devices or units, which can be electrical, mechanical or other forms.

[0100] The units described as separate components may or may not be physically separated, and the components shown as units may or may not be physical units, that is, they may be located in one place or distributed on multiple network units. Some or all of the units may be selected according to actual needs to achieve the purpose of the solution of this embodiment.

[0101] The embodiments described above are only used to illustrate the technical solutions of the present invention, rather than to limit the same. Although the present invention has been described in detail with reference to the aforementioned embodiments, those skilled in the art should understand that the technical solutions described in the aforementioned embodiments may still be modified, or some of the technical features may be replaced by equivalents. Such modifications or replacements do not deviate the essence of the corresponding technical solutions from the spirit and scope of the technical solutions of the embodiments of the present invention, and should all be included in the protection scope of the present invention.

Claims

1. A pressure compensation control method for a respiratory device, characterized in that: include: Obtaining the tidal volume and gas flow rate of the breathing gas of the user of the breathing device at the current moment; Setting a tidal volume weight parameter for controlling the tidal volume at a next moment, and a gas flow rate weight parameter for controlling the gas flow rate at a next moment; According to the product of the tidal volume weight parameter and the tidal volume, the tidal volume compensation amount at the next moment is obtained; according to the product of the gas flow rate weight parameter and the gas flow rate, the gas flow rate compensation amount at the next moment is obtained; according to the sum of the tidal volume compensation amount and the gas flow rate compensation amount, the airway pressure compensation amount at the next moment is obtained; The output pressure value of the respiratory device is obtained, and pressure compensation is performed on the output pressure value of the respiratory device at the next moment according to the output pressure value and the airway pressure compensation amount at the current moment.

2. The pressure compensation control method of the respiratory device according to claim 1, characterized in that: The setting of the tidal volume weight parameter for controlling the tidal volume at the next moment and the gas flow rate weight parameter for controlling the gas flow rate at the next moment include: Obtain the airway resistance and elastic resistance of the user of the respiratory device at the current moment; A tidal volume weight parameter is obtained according to the airway resistance and a preset airway resistance threshold, and a gas flow rate weight parameter is obtained according to the elastic resistance and a preset elastic resistance threshold.

3. The pressure compensation control method of the respiratory device according to claim 2, characterized in that: The step of obtaining a tidal volume weight parameter according to the airway resistance and a preset airway resistance threshold comprises: Obtaining an airway resistance difference according to a difference between the airway resistance and a preset airway resistance threshold; The tidal volume weight parameter is obtained according to the ratio of the airway resistance difference to a preset airway resistance threshold.

4. The pressure compensation control method of a respiratory device according to claim 1, characterized in that: The obtaining of the gas flow rate weight parameter according to the elastic resistance and the preset elastic resistance threshold comprises: converting the elastic resistance into an elastic resistance compliance value, and converting the preset elastic resistance threshold into a preset elastic resistance compliance threshold; Obtaining a compliance difference value according to a difference between the elastic resistance compliance value and the preset elastic resistance compliance threshold value; The gas flow rate weight parameter is obtained according to the ratio of the compliance difference to a preset elastic resistance compliance threshold.

5. The pressure compensation control method of a respiratory device according to claim 1, characterized in that: The setting of the tidal volume weight parameter for controlling the tidal volume at the next moment and the gas flow rate weight parameter for controlling the gas flow rate at the next moment include: Obtain the respiratory muscle pressure value of the user of the respiratory device at the current moment; The tidal volume weight parameter and the gas flow rate weight parameter are obtained according to the respiratory muscle pressure value and the preset respiratory muscle pressure threshold, and the tidal volume weight parameter and the gas flow rate weight parameter are equal.

6. The pressure compensation control method of a respiratory device according to claim 1, characterized in that: The setting of the tidal volume weight parameter for controlling the tidal volume at the next moment and the gas flow rate weight parameter for controlling the gas flow rate at the next moment include: A pressure adjustment instruction issued by a user is obtained, and the tidal volume weight parameter and the gas flow rate weight parameter are determined according to the pressure adjustment instruction, and the tidal volume weight parameter and the gas flow rate weight parameter are equal.

7. A pressure compensation control device for a breathing apparatus, characterized in that: include: An acquisition module, used to acquire the tidal volume and gas flow rate of the breathing gas of the user of the breathing device at the current moment; A weight module, used for setting a tidal volume weight parameter for controlling the tidal volume at a next moment, and a gas flow rate weight parameter for controlling the gas flow rate at a next moment; A compensation module, configured to obtain a tidal volume compensation amount at a next moment according to the product of the tidal volume weight parameter and the tidal volume; obtain a gas flow rate compensation amount at a next moment according to the product of the gas flow rate weight parameter and the gas flow rate; and obtain an airway pressure compensation amount at a next moment according to the sum of the tidal volume compensation amount and the gas flow rate compensation amount; The output module is used to obtain the output pressure value of the respiratory device, and perform pressure compensation on the output pressure value of the respiratory device at the next moment according to the output pressure value and the airway pressure compensation amount at the current moment.

8. The pressure compensation control device of the breathing apparatus according to claim 7, characterized in that: The weight module comprises: The parameter acquisition submodule is used to obtain the airway resistance and elastic resistance of the user of the respiratory device at the current moment; The weight calculation submodule is used to obtain a tidal volume weight parameter according to the airway resistance and a preset airway resistance threshold, and to obtain a gas flow rate weight parameter according to the elastic resistance and a preset elastic resistance threshold.

9. A respiratory device comprising a memory, a processor, and a machine program stored in the memory and executable on the processor, characterized in that: When the processor executes the machine program, the steps of the pressure compensation control method of the respiratory device according to any one of claims 1 to 6 are implemented.

10. A readable storage medium storing a machine program, characterized in that: When the machine program is executed by a processor, the steps of the pressure compensation control method of the respiratory device according to any one of claims 1 to 6 are implemented.

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