A pressure compensation control method, device, equipment and medium of a breathing apparatus

Abstract

The application discloses a pressure compensation control method, device, equipment and medium of a breathing apparatus, comprising: acquiring a tidal volume of a user using the breathing apparatus and a gas flow rate of breathing gas at a current time; setting a tidal volume weight parameter for controlling a tidal volume at a next time and a gas flow rate weight parameter for controlling a gas flow rate at the next time; obtaining a tidal volume compensation amount at the next time according to the product of the tidal volume weight parameter and the tidal volume; obtaining a gas flow rate compensation amount at the next time according to the product of the gas flow rate weight parameter and the gas flow rate; obtaining an airway pressure compensation amount at the next time according to the sum of the tidal volume compensation amount and the gas flow rate compensation amount; and performing pressure compensation on an output pressure value of the breathing apparatus at the next time according to the acquired output pressure value and the airway pressure compensation amount at the current time. The application solves the problem that the constant pressure support provided by the ventilation mode of the existing breathing apparatus is easy to cause insufficient ventilation support or excessive support.

Description

TECHNICAL FIELD

[0001] The present application relates to the field of automation control, and in particular to a pressure compensation control method, device, equipment and medium of a breathing apparatus. BACKGROUND

[0002] The breathing apparatus refers to a device capable of assisting or replacing the respiratory function of the human body, mainly including medical instruments such as breathing machines and anesthesia machines. The breathing apparatus plays a vital role in modern medicine. They can assist or replace the respiratory function of the human body and provide necessary breathing support for users. These devices play an important role in medical first aid, home care and other fields.

[0003] The current commonly used ventilation mode in the breathing apparatus still has some deficiencies in correcting the physiological change relationship between the patient's inspiratory force and the ventilation effect. The inspiratory resistance of the respiratory muscle is constantly changing with the inhalation and exhalation of the lung and the inspiratory flow. The size of the inspiratory and expiratory force of the respiratory muscle has no effect on the pressure support set by the breathing machine, but the pressure support provided by the existing breathing machine is constant. As a result, there is insufficient or excessive ventilation support, resulting in man-machine confrontation and causing damage to the lungs of the patient. SUMMARY

[0004] The embodiments of the present application provide a pressure compensation control method, device, equipment and medium of a breathing apparatus to solve the problem that the constant pressure support provided by the ventilation mode of the existing breathing apparatus is easy to cause insufficient or excessive ventilation support.

[0005] In a first aspect, a pressure compensation control method of a breathing apparatus is provided, comprising:

[0006] Obtaining the tidal volume of a user using the breathing apparatus and the gas flow rate of respiratory gas at the current time;

[0007] Setting a tidal volume weight parameter for controlling the tidal volume at the next time, and a gas flow rate weight parameter for controlling the gas flow rate at the next time;

[0008] According to the product of the tidal volume weight parameter and the tidal volume, a tidal volume compensation amount at the next time is obtained. According to the product of the gas flow rate weight parameter and the gas flow rate, a gas flow rate compensation amount at the next time is obtained. According to the sum of the tidal volume compensation amount and the gas flow rate compensation amount, an airway pressure compensation amount at the next time is obtained.

[0009] Obtaining the output pressure value of the breathing apparatus, and performing pressure compensation on the output pressure value of the breathing apparatus at the next time according to the output pressure value and the airway pressure compensation amount at the current time.

[0010] In a second aspect, a pressure compensation control device of a breathing apparatus is provided, comprising:

[0011] An acquisition module, configured to acquire the tidal volume and the gas flow rate of the respiratory gas of the user of the respiratory device at the current moment;

[0012] a weight module, configured to set 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;

[0013] a compensation module, configured to obtain a tidal volume compensation amount at a next moment based on the product of the tidal volume weight parameter and the tidal volume; obtain a gas flow rate compensation amount at a next moment based on 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 based on the sum of the tidal volume compensation amount and the gas flow rate compensation amount;

[0014] 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.

[0015] 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 respiratory device when executing the machine program.

[0016] 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 respiratory device are implemented.

[0017] The above-mentioned pressure compensation control method, device, equipment and medium for respiratory equipment have the following beneficial effects:

[0018] 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.

[0019] The present invention assigns a tidal volume weight parameter to the tidal volume and a gas flow rate weight parameter to the gas flow rate, and dynamically adjusts the compensation amounts of the tidal volume and gas flow rate in real time according to the set tidal volume weight parameter and gas flow rate weight parameter. Pressure compensation of the output pressure value of the respiratory device is achieved based on the dynamically adjusted tidal volume and gas flow rate compensation amounts, thereby improving or resolving the human-machine conflict and 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 existing respiratory devices is prone to insufficient or excessive ventilation support, thereby causing lung damage to the patient. BRIEF DESCRIPTION OF THE DRAWINGS

[0020] In order to more clearly illustrate the technical solutions of the embodiments of the present invention, the following briefly introduces the drawings required for use in the description of the embodiments of the present invention. Obviously, the drawings described below are only some embodiments of the present invention. For ordinary technicians in this field, other drawings can be obtained based on these drawings without creative work.

[0021] Figure 1 2. It is a schematic diagram of an application environment of a pressure compensation control method for a respiratory device according to an embodiment of the present invention;

[0022] Figure 2 is a flow chart of a pressure compensation control method for a respiratory device according to an embodiment of the present invention;

[0023] Figure 3 is a schematic diagram of a pressure compensation control device for a respiratory apparatus according to an embodiment of the present invention;

[0024] Figure 4 FIG. 1 is a schematic diagram of a breathing apparatus according to an embodiment of the present invention. DETAILED DESCRIPTION

[0025] The following will clearly and completely describe the technical solutions in the embodiments of the present invention in conjunction with the accompanying drawings. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of them. All other embodiments obtained by ordinary technicians in this field based on the embodiments of the present invention without making any creative efforts shall fall within the scope of protection of the present invention.

[0026] 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 the pressure compensation control system of the respiratory device, and the pressure compensation control system of the respiratory device includes: Figure 1The client and server shown communicate with each other over a network to address the problem that the constant pressure support provided by the ventilation mode of existing respiratory equipment can easily lead to insufficient or excessive ventilation support, thereby causing lung damage to the user. 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 is not limited to, various personal computers, laptops, smartphones, tablets, and portable wearable devices. The server can be implemented as a standalone server or a server cluster consisting of multiple servers.

[0027] In one embodiment, if Figure 2 FIG. 1 is a pressure compensation control method for a respiratory device disclosed in an embodiment of the present invention, comprising the following steps:

[0028] S01: Obtaining the tidal volume and gas flow rate of the respiratory gas of the user of the respiratory device at the current moment.

[0029] In this embodiment, tidal volume refers to the volume of gas inhaled or exhaled during each breath, typically expressed in milliliters. Tidal volume is the amount of gas delivered to the user's lungs during each breath during mechanical ventilation. It is affected by many factors, including age, gender, volume surface area, breathing habits, and body metabolism. It is the basis for assessing lung function and ventilation efficiency. During natural breathing or mechanical ventilation, tidal volume is typically measured by changes in lung volume and pressure.

[0030] 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. The flow sensor is installed 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.

[0031] When selecting a flow sensor, choose the appropriate one based on the type of respiratory device and the user's specific needs. Properly install the flow sensor in the respiratory device's airway system to ensure it accurately measures gas flow. When the user breathes, gas passes through the flow sensor, which converts the gas flow rate into an electrical signal. These signals are processed by a signal processing circuit and converted into digital signals for subsequent calculations and analysis.

[0032] Specifically, in this embodiment, a flow sensor performs real-time sampling (typically approximately every 8 milliseconds for a ventilator). The collected flow signal is integrated over a complete respiratory cycle (including both the inhalation and exhalation phases) to obtain the total volume of gas inhaled or exhaled, i.e., the tidal volume. The specific calculation method may involve real-time compensation of the flow signal to eliminate the effects of interfering factors such as pressure and temperature on the measurement results. The calculated tidal volume is typically displayed on the respiratory device's display screen for the user to review.

[0033] In this embodiment, the same flow sensor described above is used to collect the 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.

[0034] 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.

[0035] Specifically, this embodiment assigns a tidal volume weight parameter to the tidal volume to control and balance the compensation of tidal volume to the output pressure value of the respiratory device. Similarly, a gas flow rate weight parameter is assigned to the gas flow rate to control and balance the compensation of gas flow rate to the output pressure value of the respiratory device. When the gas flow rate and tidal volume of the user's breathing gas require assistance, the weight parameter can be used to control the provision of pressure support proportional to the inspiratory force. This is equivalent to amplifying the user's instantaneous inspiratory force, allowing the respiratory device to provide pressure support synchronized with this amplified instantaneous inspiratory force, thereby improving or resolving the patient-ventilator conflict and the phenomenon of insufficient or excessive ventilation, thereby improving the quality of mechanical ventilation.

[0036] 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.

[0037] Considering that the ventilation mechanism of the lungs is the result of the combined effects of the dynamics and resistance of gas flow. The driving force of inspiration comes from the contraction of inspiratory muscles such as the diaphragm, and the resistance includes airway resistance Rr and elastic resistance Re. The pressure required to overcome the airway resistance Rr during inspiration is proportional to the gas flow rate Ft, and the pressure required to overcome the elastic resistance Re of the lungs during inspiration is proportional to the tidal volume Vt. Secondly, pressure support is equivalent to amplifying the user's instantaneous inspiratory force. Through real-time sampling via the flow sensor of the respiratory device (generally, a ventilator takes approximately one sample every 8 ms), when the user's inspiratory flow rate and tidal volume require assistance, providing a pressure support proportional to the intrathoracic pressure Pm generated by the contraction of the respiratory muscles is equivalent to amplifying the user's instantaneous inspiratory force, which is the dynamic pressure that needs to be compensated, thereby achieving dynamic compensation.

[0038] The pressure at which the user's inspiratory muscle force overcomes airway resistance (Rr) The calculation formula is:

[0039]

[0040] 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.

[0041] When a user breathes using a breathing device, they need to overcome the elastic resistance Re of the lungs. The calculation formula is:

[0042]

[0043] in, To overcome the elastic resistance of the lungs, is the tidal volume, is elastic resistance, C is compliance, and Re is expressed in cmH2O / L. Therefore, the pressure required to be applied at the moment of breathing is:

[0044] (1)

[0045] in, The pressure required to breathe at the moment, 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, Rr is the elastic resistance. Based on 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.

[0046] When the user breathes spontaneously, the only pressure provided is the pressure Pm generated by the respiratory muscles. Therefore, the pressure required to be applied at the moment of breathing is:

[0047] (2)

[0048] 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, is elastic resistance.

[0049] 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:

[0050] (3)

[0051] 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 elastic resistance.

[0052] According to formula (3), the pressure generated by the respiratory muscles is:

[0053] (4)

[0054] Where Pm is the pressure generated by the respiratory muscles, The pressure required to breathe at the moment, 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:

[0055] (5)

[0056] 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 Ft.

[0057] Will and Substituting the calculation formulas (1) and (5) into formula (4), the relevant calculation formula for Pm can be obtained as follows:

[0058] (6)

[0059] 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 cmH2O / L, the same as the elastic resistance. K2 is the ratio of Paw to inspiratory flow rate Ft, and its unit is cmH2O / L / s, the same as the viscous resistance.

[0060] In order to improve or resolve the human-machine confrontation, it is necessary to make Pm=0 as much as possible. Therefore, the airway pressure Paw generated by the respiratory device is:

[0061] (7)

[0062] in, 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, C is the compliance, is the gas flow rate auxiliary pressure, is the tidal volume assist pressure.

[0063] In this embodiment, the flow sensor measures Vt and Ft at the current sampling moment and compensates them during the next flow sensor sampling interval. A breathing cycle of the respiratory device is divided into t0, t1, ..., 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):

[0064] (8)

[0065] 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 the 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.

[0066] Therefore, according to the above formula (8), when the user's inspiratory flow rate and tidal volume need to be assisted, a pressure support proportional to the intrathoracic pressure Pm generated by the contraction of the respiratory muscles can be provided to the user by setting a suitable value for K1 and K2. This pressure support is the dynamic pressure that the user needs to compensate. Specifically, the tidal volume obtained in the above step S01 (i.e. ) and the tidal volume weight parameter (ie 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 (ie ) 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:

[0067]

[0068] 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.

[0069] S04: Obtaining an output pressure value of the respiratory device, and performing pressure compensation on an 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.

[0070] Specifically, when dynamic pressure compensation is turned on, at each moment of inspiration, 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 by the set airway pressure. Enhancement is to add an airway pressure compensation value based on the airway pressure value provided by the original respiratory equipment 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 amount is subtracted from the airway pressure value provided by the original breathing device. The pressure value of the airway pressure is adjusted to the next output pressure of the respiratory device. When the respiratory device detects that the sum of inspiratory muscle force and airway pressure is lower than the elastic recoil pressure of the respiratory system, inspiration ends and exhalation begins, completing a respiratory cycle. This pressure compensation cycle provides ventilation assistance. By assisting airway pressure, the user controls the breathing pattern of each respiratory cycle, while inspiratory muscle force determines the start, maintenance, and termination of ventilator air delivery. Spontaneous breathing and ventilator air delivery can be synchronized. Users can adjust the breathing pattern according to their different ventilation needs.

[0071] Dynamic pressure compensation is a form of assisted ventilation that requires the user to breathe normally. According to the above principle and method, if the user does not breathe spontaneously, 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 assisted ventilation function, apnea ventilation backup should be set, and an apnea alarm should be set to ensure the safety of using the dynamic pressure compensation auxiliary function; in addition, in clinical practice, if the user's breathing work is unstable or the breathing circuit vibrates, it is very easy to trigger ventilation falsely when using high auxiliary ratios K1 and K2 values, so the values ​​of K1 and K2 should not be too high.

[0072] The following examples illustrate how to adjust breathing patterns in several specific situations: For patients with chronic obstructive pulmonary disease (COPD), increased airway resistance and functional residual capacity lead to airway occlusion. This gas blockage generates intrinsic positive end-expiratory pressure (PEEPi). Inspiratory muscles must first overcome the intrinsic PEEP to open the occluded airway before inspiratory flow can occur. During the initial and final stages of inspiration, inspiratory pressure changes significantly, while lung volume increases only slightly. During dynamic pressure compensation (DPC) ventilation, if positive end-expiratory pressure (PEEP) is not set simultaneously, respiratory muscle force (Pm) must first overcome the intrinsic PEEP to trigger ventilation, which in turn weakens ventilatory support to varying degrees. Therefore, when using DPC for COPD, the set PEEP should be used first to dilate the occluded airway. The generally set positive end-expiratory pressure is generally 80% of the intrinsic 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 with 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 phase, 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.

[0073] The main purpose of this invention is to provide a pressure compensation 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 is obtained based on the set weight parameters and the user's instantaneous inspiratory force. , allowing respiratory equipment to provide synchronized pressure support to users, thereby improving or resolving human-machine conflict, as well as insufficient or excessive ventilation, and thus improving the quality of mechanical ventilation.

[0074] In one embodiment, the above-mentioned step S02, i.e., 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, includes the following steps:

[0075] S201: Obtain the airway resistance and elastic resistance of the respiratory device user at the current moment.

[0076] Airway resistance in this embodiment refers to the resistance generated when gas flows through the respiratory tract, which is the pressure difference generated by a unit flow rate. It reflects the degree of obstruction encountered by gas when flowing in the respiratory tract. The following are several commonly used airway resistance measurement methods:

[0077] 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 that alveolar pressure is balanced with airway opening pressure. By rapidly occluding the respiratory passages and recording the flow rate before occlusion and the pressure after occlusion, airway resistance can be calculated. The main advantage of this method is its simplicity and convenience, making it suitable for both routine measurement and clinical monitoring.

[0078] 2) Mechanical ventilation measurement directly measures airway resistance during mechanical ventilation. The basic principle is to calculate airway resistance by measuring peak airway pressure and airflow velocity according to fluid dynamics formulas. The specific formula is: Airway resistance = Peak airway pressure / Airflow velocity. This method enables real-time and continuous monitoring of changes in airway resistance, which is important for assessing respiratory system function and guiding mechanical ventilation therapy.

[0079] 3) Esophageal manometry indirectly measures airway resistance by placing a manometric catheter in the esophagus. This method measures the intraesophageal pressure at the onset of inspiratory flow, equivalent to the pressure at the end of expiration, known as PEEPi (intrinsic positive end-expiratory pressure). Although esophageal manometry does not directly measure airway resistance, it provides information on pressures related to airway resistance and helps assess respiratory function.

[0080] The elastic resistance in this embodiment refers to the elastic resistance of alveolar expansion, including the elastic recoil force and surface tension of the alveoli. It is the resistance to inhalation and the driving force for exhalation. The following methods are commonly used to measure lung elastic resistance:

[0081] 1) Direct measurement is to calculate lung elastic resistance by measuring changes in lung volume and transpulmonary pressure. This method requires specialized equipment and operating techniques.

[0082] 2) Indirect measurement involves measuring the compliance of the respiratory system to indirectly estimate lung elastic resistance. Compliance is the respiratory system's ability to respond to changes in pressure and is inversely proportional to the elastic resistance. Therefore, lung elastic resistance can be indirectly assessed by measuring compliance.

[0083] This embodiment measures airway resistance (Rr) using the aforementioned mechanical ventilation measurement method. First, during mechanical ventilation, the monitoring function on the respiratory device is used to record the user's peak inspiratory pressure (Ppeak), plateau pressure (Pplat), and corresponding inspiratory flow (Flow). Peak inspiratory pressure is the highest pressure during ventilator air delivery, plateau pressure is the airway pressure at the end of an inspiratory hold (with the inspiratory and expiratory valves closed and airflow at zero), and inspiratory flow is the flow rate of gas through the respiratory tract. Airway resistance (Rr) is then calculated based on the measured peak inspiratory pressure (Ppeak), plateau pressure (Pplat), and corresponding inspiratory flow (Flow). The formula for calculating airway resistance (Rr) is:

[0084]

[0085] in, is the airway resistance, Ppeak is the peak inspiratory pressure, and Pplat is the plateau pressure. is the inspiratory flow.

[0086] This embodiment uses the above-mentioned indirect measurement method to estimate 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 inspiration phase, which reflects the pressure in the alveoli. The end-expiratory pressure is the pressure remaining in the airway at the end of the expiration phase. Then, the compliance is calculated based on the measured tidal volume Vt, the inspiration plateau pressure Pplat, and the end-expiratory pressure PEEP. The relevant calculation formula for the respiratory system compliance C is:

[0087]

[0088] 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:

[0089]

[0090] Among them, Re is the elastic resistance and C is the compliance.

[0091] S202: Obtaining a tidal volume weight parameter according to the airway resistance and a preset airway resistance threshold, and obtaining a gas flow rate weight parameter according to the elastic resistance and the preset elastic resistance threshold.

[0092] 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:

[0093] In this embodiment, the airway resistance threshold is set based on the normal value of airway resistance. The normal 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 unified standard for the specific normal range. Some literature and studies may provide specific ranges, but these ranges may vary depending on different measurement methods, instruments, and populations.

[0094] For adults, normal airway resistance ranges from 1 to 3 cmH2O / (L / s), but this can vary between studies. For children, the normal range of airway resistance may vary with age and is generally slightly higher than that of adults.

[0095] Therefore, when setting the airway resistance threshold, multiple attempts can be made based on the user's specific situation to ensure that the user's breathing is smooth.

[0096] The gas flow rate weight parameter is calculated based on the elastic resistance obtained in step S01 and the pre-set elastic resistance threshold. Calculating the gas flow rate weight parameter may include:

[0097] In this embodiment, the airway resistance threshold is set based on the normal value of elastic resistance. However, lung elastic resistance can be expressed using lung compliance, which is the ratio of the change in lung volume to the change in transpulmonary pressure. The compliance of a normal adult lung is approximately 2.0 L / kPa (or 0.2 L / cmH2O). This means that for every 1 kPa (or 1 cmH2O) change in transpulmonary pressure, the lung volume can change by 2.0 L (or 0.2 L). Lung compliance is inversely proportional to elastic resistance: the greater the compliance, the lower the elastic resistance; conversely, the lower the compliance, the greater the elastic resistance. However, when setting the elastic resistance threshold, multiple trials can be performed based on the user's specific situation to ensure smooth breathing.

[0098] The pressure compensation control method of the respiratory device of this embodiment takes into account the interaction of two factors in lung ventilation, when setting the tidal volume weight parameter and the gas flow rate weight parameter by using airway resistance and elastic resistance. One is the power of inspiration, which is the pressure of gas flow; the other is the resistance that prevents gas flow, which 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, 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 by using airway resistance and elastic resistance, the calculation result of the airway pressure compensation amount can be made more accurate, thereby allowing the respiratory equipment to provide users with more accurate pressure support, further improving the quality of mechanical ventilation.

[0099] In one embodiment, the above-mentioned 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:

[0100] S301: Obtain an airway resistance difference according to a difference between the airway resistance and a preset airway resistance threshold.

[0101] Specifically, the user's current airway resistance obtained in step S202 is subtracted from the preset airway resistance threshold to obtain an airway resistance difference. The airway resistance difference is a measure of the difference between the actual airway resistance and the preset airway resistance threshold. It can reflect in real time whether the user's airway resistance deviates from the preset standard. In this embodiment, the airway resistance difference is a scalar value, which has only magnitude but no direction.

[0102] S302: Obtaining the tidal volume weight parameter according to the ratio of the airway resistance difference to a preset airway resistance threshold.

[0103] 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:

[0104]

[0105]

[0106] in, is the tidal volume weight parameter, is the difference in airway resistance, is the preset airway resistance threshold, The user's current airway resistance.

[0107] The calculation process of tidal volume weight parameter is further explained below with 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 is for:

[0108]

[0109]

[0110] Among them, the normal value 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 by 3 cmH2O / L / s. Therefore, based on the above calculation results, K1 is set to 0.75 cmH2O / L / s.

[0111] The present invention calculates the change in airway resistance at the current moment relative to a preset airway resistance threshold, and then derives a tidal volume weighting parameter based on the ratio of this change to the preset airway resistance threshold. Because the intrathoracic pressure required during inspiration is closely related to airway resistance, the tidal volume is adaptively adjusted based on the real-time changes in airway resistance to ensure stable ventilation efficiency. When airway resistance increases, the tidal volume weighting parameter is increased to compensate for the decrease in ventilation volume caused by the increased resistance, thereby maintaining adequate ventilation and further improving the quality of mechanical ventilation.

[0112] In one embodiment, the above-mentioned 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:

[0113] 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.

[0114] This embodiment takes into account that the magnitude of elastic resistance is affected by many factors. If a direct measurement method is used to directly measure the magnitude of elastic resistance, it would be difficult and the measurement results would be inaccurate. Therefore, this embodiment converts elastic resistance into lung compliance. Compliance is the ability of the respiratory system to respond to pressure changes and is inversely proportional to elastic resistance. Therefore, by measuring compliance, the magnitude of changes in lung elastic resistance can be indirectly assessed. The specific conversion formula between elastic resistance and compliance is:

[0115]

[0116] Among them, Re is the elastic resistance and C is the compliance.

[0117] S402: Obtaining a compliance difference value according to a difference between the elastic resistance compliance value and the preset elastic resistance compliance threshold value.

[0118] The compliance difference is a measure of the difference between the actual elastic resistance compliance value and a 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 step S401 from the preset elastic resistance compliance threshold. In this embodiment, the compliance difference is a scalar value, which has only magnitude but no direction.

[0119] S403: Obtaining the gas flow rate weight parameter according to the ratio of the compliance difference to a preset elastic resistance compliance threshold.

[0120] Specifically, the ratio between the compliance difference obtained in step S402 and the preset elastic resistance compliance threshold is calculated to obtain the gas flow rate weight parameter. The specific calculation formula is:

[0121]

[0122]

[0123] 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.

[0124] The calculation process of the gas flow rate weight parameter is further explained below using specific numerical values. Assuming that the compliance decreases from 100 ml / cmH2O to 29 ml / cmH2O, the corresponding compliance difference is:

[0125]

[0126]

[0127] 100 ml / cmH2O is the preset elastic resistance compliance threshold N2. This compliance difference indicates that the current elastic resistance compliance value deviates from the preset elastic resistance compliance threshold of 71 mL / cmH2O. Therefore, K2 is set to 0.71 cmH2O / L / s.

[0128] The pressure compensation control method for a respiratory device in this embodiment converts elastic resistance into a compliance value, obtains a gas flow rate weight parameter based on the elastic resistance compliance value and a preset elastic resistance compliance threshold, and then calculates the gas flow rate weight parameter based on the ratio of the compliance difference to the preset elastic resistance compliance threshold. Because the magnitude of elastic resistance is affected by multiple factors, direct measurement of the magnitude of elastic resistance is difficult and inaccurate. Therefore, this embodiment converts elastic resistance into lung compliance to calculate the gas flow rate weight parameter, which can make the calculation result of the weight parameter more accurate, enable more precise control of the gas flow rate, thereby maintaining adequate ventilation and further improving the quality of mechanical ventilation.

[0129] In one embodiment, the above-mentioned step S02, i.e., 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, includes the following steps:

[0130] S501: Obtain the respiratory muscle pressure value of the respiratory device user at the current moment.

[0131] The respiratory muscle pressure in this embodiment refers to the force generated by the respiratory muscles during the breathing process, which is the power source of respiratory movement. The respiratory muscles include inspiratory muscles and expiratory muscles. The inspiratory muscles are mainly the diaphragm and external intercostal muscles, which expand the thorax by contracting, producing the inhalation movement; the expiratory muscles are mainly the abdominal muscles and internal intercostal muscles, which shrink the thorax by contracting, producing the exhalation movement. The magnitude of 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, airway resistance, etc. When the respiratory muscles contract, they generate a certain amount of pressure, which is the power that pushes gas in and out of the lungs. Under normal circumstances, the respiratory muscle pressure and the pressure in the lungs are balanced, allowing respiratory movement to proceed smoothly.

[0132] However, in some cases, respiratory muscle pressure may change. For example, when suffering from respiratory diseases or neuromuscular diseases, the respiratory muscles may be damaged, resulting in a decrease in respiratory muscle strength and respiratory muscle pressure, thereby affecting respiratory function. Therefore, this embodiment controls the pressure value output by the compensation respiratory device by detecting changes in respiratory muscle pressure to provide respiratory support for the user.

[0133] Respiratory muscle pressure can be measured in a variety of ways, including the following:

[0134] Esophageal pressure (Pes) is the gold standard for assessing respiratory muscle pressure. By inserting an esophageal pressure catheter into the esophagus, changes in esophageal pressure can be measured, indirectly reflecting the pressure of the respiratory muscles (primarily the diaphragm). Esophageal pressure measurement allows the calculation of respiratory muscle pressure, which is the difference between the static chest wall recoil pressure and the total esophageal pressure. Furthermore, the esophageal pressure-time product is also an important indicator for assessing respiratory muscle energy expenditure.

[0135] Diaphragm electrical activity (EAdi) monitoring uses electrodes placed in the esophagus to monitor the electrical activity of the diaphragm. EAdi is closely related to diaphragmatic pressure and varies proportionally with the level of respiratory assistance. By monitoring EAdi, the user's respiratory drive and respiratory muscle effort can be assessed. EAdi values ​​can also be converted to conventional respiratory muscle pressure by calculating neuromuscular efficiency (i.e., the ratio of the airway pressure drop to EAdi).

[0136] This embodiment obtains the respiratory muscle pressure value of the respiratory device user at the current moment by using the esophageal pressure measurement method.

[0137] 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.

[0138] 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 value; and then obtains the tidal volume weight parameter based on the ratio of the respiratory muscle pressure difference value to the preset elastic resistance threshold value. The tidal volume weight parameter is set equal to the gas flow rate weight parameter. The specific calculation formula is:

[0139]

[0140] in, is the gas velocity weight parameter, is the tidal volume weight parameter, N3 is the preset respiratory muscle pressure threshold, It is the user's respiratory muscle pressure value at the current moment.

[0141] 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 as follows:

[0142]

[0143] in, is the user's respiratory muscle pressure value 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.

[0144] The pressure compensation control method for the respiratory device of this embodiment obtains a tidal volume weight parameter and a gas flow rate weight parameter by comparing the respiratory muscle pressure value with a 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 volutrauma, and further improving the quality of mechanical ventilation.

[0145] In one embodiment, the above-mentioned step S02, i.e., 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, includes the following steps:

[0146] 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.

[0147] 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.

[0148] In this embodiment, the user issues a pressure adjustment command through the interface or controller handle of the respiratory device. The user enters 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 read tidal volume weight parameter and gas flow rate weight parameter settings to calculate the airway pressure compensation amount. .

[0149] 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 or controller handle of the respiratory device to reduce the air supply volume and air supply speed, thereby reducing the airway pressure compensation amount and thus 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 or controller handle of the respiratory device to increase the air supply volume and air supply speed, thereby increasing the airway pressure compensation amount and thus 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.

[0150] 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 pressure adjustment instructions. Through the pressure adjustment instructions, the user can fine-tune the ventilation support by dynamically adjusting the weight parameters of the tidal volume and gas flow rate according to his or her own breathing experience and needs, 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.

[0151] It should be understood that the size of the serial numbers of the steps in the above embodiments does not 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 embodiments of the present invention.

[0152] In one embodiment, a pressure compensation control device for a respiratory device is provided, which 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 functional modules are described in detail as follows:

[0153] The acquisition module is used to obtain the tidal volume and gas flow rate of the respiratory gas of the user of the respiratory device at the current moment.

[0154] 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.

[0155] The compensation module is used to obtain the tidal volume compensation amount at the next moment according to the product of the tidal volume weight parameter and the tidal volume; obtain the gas flow rate compensation amount at the next moment according to the product of the gas flow rate weight parameter and the gas flow rate; and obtain the 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.

[0156] 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.

[0157] The main purpose of this invention is to provide a pressure compensation 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 is obtained based on the set weight parameters and the user's instantaneous inspiratory force. , allowing respiratory equipment to provide synchronized pressure support to users, thereby improving or resolving human-machine conflict, as well as insufficient or excessive ventilation, and thus improving the quality of mechanical ventilation.

[0158] The specific definition of the pressure-compensating control device for a respiratory device can be found in the definition of the pressure-compensating control method for a respiratory device described above and will not be further elaborated here. The various modules within the pressure-compensating control device for a respiratory device described above may be implemented in whole or in part via software, hardware, or a combination thereof. These modules may be embedded in or independent of a processor within the device in hardware form, or stored in memory within the device in software form, allowing the processor to call and execute the corresponding operations of each module.

[0159] In one embodiment, Figure 4 This is a structural diagram of a respiratory device provided by the fourth embodiment of the present invention. Figure 4 As shown, the respiratory 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 apparatus are implemented.

[0160] The respiratory device may include, but is not limited to, a processor and a memory. It will be understood by those skilled in the art 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.

[0161] The processor may be a CPU, other general-purpose processors, a digital signal processor (DSP), an application-specific integrated circuit (ASIC), a field-programmable gate array (FPGA), 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.

[0162] Memory includes readable storage media, internal memory, and other components. Internal memory can be the internal memory of a machine device, providing an environment for the operation of the operating system and machine-readable instructions stored in the readable storage medium. The readable storage medium can be the machine device's hard drive. In other embodiments, it can also be an external storage device, such as a plug-in hard drive, a Smart Media Card (SMC), a Secure Digital (SD) card, or a flash memory card. Furthermore, memory can include both the machine device's internal storage unit and external storage devices. Memory is used to store the operating system, application programs, boot loaders, data, and other programs, such as the program code of machine programs. Memory can also be used to temporarily store data that has been output or is about to be output.

[0163] Those skilled in the art can clearly understand that, for the convenience and brevity of description, only the above-mentioned division of each functional unit and module is exemplified, and in actual application, the above-mentioned functions can be completed by different functional units and modules according to needs, 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. Each functional unit and module in the embodiment can be integrated in one processing unit, or each unit can exist physically, or two or more units can be integrated in one unit. The integrated unit can be realized in the form of hardware or in the form of software functional unit. In addition, the specific names of each functional unit and module are only for easy distinction, and do not limit the protection scope of the present application. The specific working process of the unit and module in the above device can refer to the corresponding process in the foregoing method embodiments, which will not be described here. If the integrated unit is realized in the form of software functional unit and sold or used as an independent product, it can be stored in a machine-readable storage medium. Based on this understanding, the present application realizes all or part of the processes in the above-mentioned embodiment methods, which can be completed by a machine program to instruct related hardware. The machine program can be stored in a machine-readable storage medium, and when the processor executes the machine program, the steps of the above-mentioned method embodiment can be realized. The machine program includes machine program code, which can be in the form of source code, object code, executable file or some intermediate form. The machine-readable medium at least includes any entity or device capable of carrying machine program code, recording medium, machine storage, read-only memory (ROM), random access memory (RAM), electrical carrier signal, telecommunication signal and software distribution medium. For example, U disk, mobile hard disk, magnetic disk or optical disk, etc. In some jurisdictions, according to legislation and patent practice, the machine-readable medium cannot be an electrical carrier signal and a telecommunication signal.

[0164] The present application realizes all or part of the processes in the above-mentioned embodiment methods, which can also be completed by a machine program product. When the machine program product runs on the breathing device, it makes the breathing device execute to realize the steps in the above-mentioned method embodiment.

[0165] In the above-mentioned embodiments, the description of each embodiment has its own emphasis, and the parts not described or recorded in detail in a certain embodiment can be referred to the related description of other embodiments.

[0166] In an embodiment, a readable storage medium is provided, and the machine-readable storage medium stores a machine program. When the machine program is executed by a processor, the pressure compensation control method of the breathing device in the above-mentioned embodiment is realized, for example Figure 2The functions of the obtaining module, the weight module, the compensating module and the output module are not repeated here to avoid repetition. Figure 3 The functions of the obtaining module, the weight module, the compensating module and the output module are not repeated here to avoid repetition.

[0167] Those skilled in the art can understand that all or part of the processes in the above-mentioned embodiment methods can be completed by a machine program instructing related hardware. 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 above-mentioned embodiment methods. Any reference to memory, storage, database or other medium used in the embodiments provided by the present application can include non-volatile and / or volatile memory. Non-volatile memory can include read-only memory (ROM), programmable ROM (PROM), electrically programmable ROM (EPROM), electrically erasable programmable ROM (EEPROM) or flash memory. Volatile memory can include random access memory (RAM) or external cache memory. As an illustration but not limitation, RAM is available in various forms, such as static RAM (SRAM), dynamic RAM (DRAM), synchronous DRAM (SDRAM), double data rate SDRAM (DDR SDRAM), enhanced SDRAM (ESDRAM), synchronous link (Synchlink) DRAM (SLDRAM), Rambus direct RAM (RDRAM), direct memory bus dynamic RAM (DRDRAM) and memory bus dynamic RAM (RDRAM) and the like.

[0168] The present application can also be implemented by a machine program product, which, when running on a breathing device, enables the breathing device to perform the steps in the above-mentioned embodiment methods.

[0169] In the above-mentioned embodiments, the description of each embodiment has its own focus. The parts not described or recorded in detail in a certain embodiment can be referred to the relevant description of other embodiments.

[0170] Those skilled in the art can realize that the units and algorithm steps of the examples described in combination with the embodiments disclosed herein can be realized by electronic hardware or a combination of computer software and electronic hardware. Whether the functions are realized by hardware or software depends on the specific application and design constraints of the technical solution. Those skilled in the art can use different methods to implement the described functions for each specific application, but such implementation should not be considered beyond the scope of the present application.

[0171] In the embodiments provided herein, 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 merely illustrative. For example, the division of modules or units is merely a logical functional division. In actual implementation, there may be other division methods, such as multiple units or components being combined or integrated into another system, or some features being ignored or not implemented. In addition, the mutual coupling or direct coupling or communication connection shown or discussed may be through some interface, indirect coupling or communication connection of devices or units, and may be electrical, mechanical, or other forms.

[0172] Units described as separate components may or may not be physically separate, and components shown as units may or may not be physical units, that is, they may be located in one place or distributed across multiple network units. Some or all of these units may be selected to achieve the purpose of this embodiment according to actual needs.

[0173] 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 they can still modify the technical solutions described in the aforementioned embodiments, or make equivalent replacements for some of the technical features therein. These modifications or replacements do not deviate the essence of the corresponding technical solutions from the spirit and scope of the technical solutions of the various embodiments of the present invention, and should all be included in the scope of protection 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 respiratory gas of the user of the respiratory 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; The tidal volume compensation amount at the next moment is obtained according to the product of the tidal volume weight parameter and the tidal volume; the gas flow rate compensation amount at the next moment is obtained according to the product of the gas flow rate weight parameter and the gas flow rate; and the airway pressure 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; An output pressure value of the respiratory device is obtained, and pressure compensation is performed on an 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.

2. 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 setting of 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 respiratory device user 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 the preset elastic resistance threshold.

3. The pressure compensation control method of the respiratory device according to claim 2, characterized in that: The obtaining of 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 2, 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 setting of 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 respiratory device user 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 setting of 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 respiratory device, characterized in that: include: An acquisition module, configured to acquire the tidal volume and the gas flow rate of the respiratory gas of the user of the respiratory device at the current moment; a weight module, configured to set 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 based on the product of the tidal volume weight parameter and the tidal volume; obtain a gas flow rate compensation amount at a next moment based on 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 based on 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 respiratory apparatus according to claim 7, characterized in that The weight module includes: The parameter acquisition submodule is used to obtain the airway resistance and elastic resistance of the respiratory device user 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, wherein: When the processor executes the machine program, the steps of the pressure compensation control method of the respiratory apparatus 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 apparatus according to any one of claims 1 to 6 are implemented.

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