Medical ventilation apparatus, control method and computer readable storage medium

Abstract

A medical ventilation device, a control method and a computer readable storage medium, the medical ventilation device comprises a gas source interface (10), a breathing circuit (20), a high-frequency oscillation generation device (30) and a controller (40), the breathing circuit (20) is connected with the gas source interface (10) and a patient pipeline (50) connected with the respiratory system of a patient respectively, the breathing circuit (20) comprises an inhalation branch, and an exhaust device (201) is arranged on the breathing circuit (20), the high-frequency oscillation generation device (30) forms high-frequency oscillation of the gas of the inhalation branch, and the controller (40) controls the high-frequency exhaust device (201) to exhaust the gas exhaled by the patient through the patient pipeline (50) when the medical ventilation device is in a high-frequency exhalation stage, so that the active exhaust can be realized through the exhaust device (201) when the medical ventilation device is in the high-frequency exhalation stage, the influence of resistance in the exhaust process is reduced, the exhaust efficiency is improved, so that the gas can be exhausted in time, and the safety of the patient is ensured.

Description

Technical Field

[0001] This invention relates to medical device technology, and more particularly to a medical ventilation device, control method, and computer-readable storage medium. Background Technology

[0002] Currently, medical ventilation equipment used to assist patients' breathing includes conventional ventilators and high-frequency ventilators. Conventional ventilators provide a respiratory rate of 4-150 breaths per minute, while high-frequency ventilators provide a respiratory rate of 240-1800 breaths per minute, in order to provide patients with more oxygen.

[0003] While providing more oxygen to patients using a high-frequency ventilator, gases such as carbon dioxide also need to be expelled. Currently, this expulsion occurs automatically during the exhalation phase through the patient's tubing (such as a mask worn by the patient). However, this automatic expulsion method is affected by the resistance of the mask, causing gas to accumulate gradually. As gas accumulates, the average pressure in the patient's tubing increases, leading to overinflation of the lungs and threatening the patient's life. Summary of the Invention

[0004] This invention provides a medical ventilation device, a control method, and a computer-readable storage medium to achieve active ventilation.

[0005] On one hand, embodiments of the present invention provide a medical ventilation device, the medical ventilation device including an air source interface, a breathing circuit, a high-frequency oscillation generating device and a controller, wherein an exhaust device is provided on the breathing circuit;

[0006] The breathing circuit is connected to the gas source interface and the patient tubing connected to the patient's respiratory system, and the breathing circuit includes an inspiratory branch.

[0007] The high-frequency oscillation generating device generates high-frequency oscillations in the gas of the intake branch;

[0008] The controller controls the exhaust device to expel the gas exhaled by the patient through the patient tubing at a high frequency when the medical ventilation device is in the high-frequency exhalation phase.

[0009] On the other hand, embodiments of the present invention provide a control method for a medical ventilation device, comprising:

[0010] The gas in the inspiratory branch of the breathing circuit is generated into high-frequency oscillation by a high-frequency oscillation generating device. The breathing circuit is connected to the gas source interface and the patient tubing connected to the patient's respiratory system.

[0011] When the medical ventilation device is in the high-frequency exhalation phase, the exhaust device is controlled to expel the gas exhaled by the patient through the patient tubing at a high frequency.

[0012] In another aspect, embodiments of the present invention provide a computer-readable storage medium storing executable instructions configured to cause a processor to execute the executable instructions to implement the control method of the above-mentioned medical ventilation device.

[0013] In this embodiment of the invention, the medical ventilation device includes a gas source interface, a breathing circuit, a high-frequency oscillation generator, and a controller. The breathing circuit is connected to the gas source interface and a patient tubing connected to the patient's respiratory system. The breathing circuit includes an inspiratory branch and is equipped with an exhaust device. The high-frequency oscillation generator generates high-frequency oscillations in the gas from the inspiratory branch. When the medical ventilation device is in the high-frequency exhalation phase, the controller controls the exhaust device to discharge the gas exhaled by the patient through the patient tubing at a high frequency. This allows the exhaust device to actively discharge gas during the high-frequency exhalation phase, reducing the resistance during the exhaust process, improving exhaust efficiency, and ensuring timely gas discharge to guarantee the patient's safety. Attached Figure Description

[0014] To more clearly illustrate the technical solutions in the embodiments of the present invention or the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are some embodiments of the present invention. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0015] Figure 1 This is a schematic diagram of the structure of a medical ventilation device provided in an embodiment of the present invention;

[0016] Figure 2 This is a schematic diagram of the inspiratory branch and high-frequency oscillation generating device in the medical ventilation device provided in an embodiment of the present invention;

[0017] Figure 3 This is another schematic diagram of the inspiratory branch and high-frequency oscillation generating device in the medical ventilation device provided in this embodiment of the invention;

[0018] Figure 4 This is a schematic diagram illustrating the effect of venting air through the existing patient tubing;

[0019] Figure 5 This is a schematic diagram illustrating the exhaust effect of the medical ventilation device provided in this embodiment of the invention;

[0020] Figure 6 This is a schematic diagram of another medical ventilation device provided in an embodiment of the present invention;

[0021] Figure 7 This is a schematic diagram of the structure of another medical ventilation device provided in an embodiment of the present invention;

[0022] Figure 8 This is a schematic diagram of a breathing circuit provided in an embodiment of the present invention;

[0023] Figure 9 This is a schematic diagram illustrating insufficient amplitude oscillation in existing technologies;

[0024] Figure 10 This is a schematic diagram of a control waveform provided in an embodiment of the present invention;

[0025] Figure 11 and Figure 12 This is a schematic diagram of the structure of another medical ventilation device provided in an embodiment of the present invention;

[0026] Figure 13 This is a flowchart of a control method for a medical ventilation device provided in an embodiment of the present invention;

[0027] Figure 14 This is a flowchart of another control method for a medical ventilation device provided in an embodiment of the present invention;

[0028] Figure 15 This is a flowchart of another control method for a medical ventilation device provided in an embodiment of the present invention;

[0029] Figure 16 This is a flowchart of another control method for a medical ventilation device provided in an embodiment of the present invention. Detailed Implementation

[0030] To make the objectives, technical solutions, and advantages of this invention clearer, the invention will be further described in detail below with reference to the accompanying drawings. This invention should not be construed as limited to the provided embodiments. On the contrary, the content described in the embodiments of this invention makes the invention comprehensive and complete, and conveys the concept of the embodiments of this invention to those skilled in the art. Therefore, other embodiments obtained by those skilled in the art without creative effort are all within the scope of protection of this invention.

[0031] It should be noted that, in the embodiments of this disclosure, the terms "comprising," "including," or any other variations thereof are intended to cover non-exclusive inclusion, such that a method or server that includes a list of elements includes not only the elements expressly described, but also other elements not expressly listed, or elements inherent to implementing the method or server. Without further limitations, an element defined by the phrase "comprising a..." does not exclude the presence of other related elements (e.g., steps in the method or units in the server, such as portions of circuitry, processors, programs, or software, etc.) in the method or server that includes that element.

[0032] For example, the medical ventilation device and control method for the medical ventilation device provided in this disclosure include a series of apparatuses and steps. However, the medical ventilation device and control method for the medical ventilation device provided in this disclosure are not limited to the steps described. It should be noted that in the following description, the term "one embodiment" refers to a subset of all possible embodiments. However, it is understood that "one embodiment" can be the same subset or a different subset of all possible embodiments, and can be combined with each other without conflict.

[0033] Before providing a further detailed description of the present invention, the nouns and terms used in the embodiments of the present invention are explained, and the nouns and terms used in the embodiments of the present invention are subject to the following interpretations:

[0034] High frequency: refers to a ventilation frequency that is more than 4 times the normal frequency (abbreviated as normal frequency). For example, in China, a frequency of 240-1800 breaths per minute is called high frequency. The U.S. Food and Drug Administration (FDA) defines high frequency as a ventilation frequency greater than 150 breaths per minute.

[0035] High-frequency exhalation phase and high-frequency inhalation phase: These are two phases of medical ventilation equipment. During the high-frequency exhalation phase, the patient is in the process of high-frequency exhalation, during which the gas exhaled by the patient through the patient tubing is expelled. During the high-frequency inhalation phase, the patient is in the process of high-frequency inhalation, during which the medical ventilation equipment generates high-frequency oscillations. Under the action of high-frequency oscillations, gas, especially oxygen, is delivered to the patient's lungs through the patient tubing.

[0036] Preset high pressure and preset low pressure: These are the maximum and minimum pressure values ​​corresponding to the breathing circuit, such as the maximum and minimum gas pressure in the patient tubing connected to the breathing circuit. The gas pressure corresponding to the breathing circuit can change between the preset high pressure and preset low pressure as the patient breathes.

[0037] Target average pressure: The average of the preset high pressure and preset low pressure.

[0038] Please see Figure 1 The diagram shows a structural schematic of a medical ventilation device provided in an embodiment of the present invention, which may include: an air source interface 10, a breathing circuit 20, a high-frequency oscillation generating device 30 and a controller 40, and an exhaust device 201 is provided on the breathing circuit 20.

[0039] The breathing circuit 20 is connected to the gas source interface 10 and the patient tubing 50, which is connected to the patient's respiratory system. The breathing circuit 20 includes an inspiratory branch. The gas source interface 10 serves as an input port for external gas, allowing external gas to be input into the inspiratory branch of the breathing circuit 20. The gas is then delivered to the patient at the end of the patient tubing via the inspiratory branch and the patient tubing 50, such as to the patient's lungs. The patient tubing 20 can be, but is not limited to, any type of mask or patient breathing interface, through which gas is delivered to the patient.

[0040] The high-frequency oscillation generating device 30 generates high-frequency oscillations in the gas of the inhalation branch, so as to deliver the gas in the inhalation branch to the patient at the end of the patient tubing under the action of high-frequency oscillations. In particular, it delivers oxygen in the inhalation branch to the patient under the action of high-frequency oscillations.

[0041] In this embodiment, the gas source interface 10 may include an oxygen source interface and an air source interface, so as to input oxygen and air into the inhalation branch respectively from the oxygen source interface and the air source interface. The high-frequency oscillation generating device 30 installed on the inhalation branch generates high-frequency oscillations between the oxygen and air, so that the oxygen can be delivered to the patient tubing under the action of high-frequency oscillations and reach the patient at the end of the patient tubing. For example, one way in which the high-frequency oscillation generating device 30 generates high-frequency oscillations is that the high-frequency oscillation generating device 30 adjusts the oxygen flow rate and air flow rate during the high-frequency inhalation stage to generate high-frequency oscillations through flow rate regulation. The high-frequency oscillation generating device 30 may be, but is not limited to, a proportional solenoid valve, a shut-off valve, an on / off valve, or other valves that can adjust the flow rate, all of which can achieve the purpose of delivering oxygen to the patient.

[0042] Correspondingly, the optional structures for the intake branch and the high-frequency oscillation generator are as follows: Figure 2 and Figure 3 As shown, in Figure 2 The middle intake branch includes an oxygen input branch 202 and an air input branch 203. The high-frequency oscillation generating device 30 includes a first high-frequency generating device 301 and a second high-frequency generating device 302. The first high-frequency generating device 301 is provided on the oxygen input branch 202, and the second high-frequency generating device 302 is provided on the air input branch 203.

[0043] The oxygen input branch 202 is connected to the oxygen source interface (O2), and oxygen input through the oxygen source interface enters the oxygen input branch 202. The air input branch 203 is connected to the air source interface (Air), and air input through the air source interface enters the air input branch 203. The first high-frequency generating device 301 and the second high-frequency generating device 302 can generate high-frequency oscillations between the oxygen in the oxygen input branch and the air in the air input branch when the medical ventilation equipment is in the high-frequency inhalation phase.

[0044] During the oxygen and air input process, the input ratio of oxygen and air can be controlled according to the patient's condition to meet their needs. For example, during the input of oxygen from the oxygen source interface and air from the air source interface, the input is carried out according to a preset oxygen and air input ratio. Simultaneously, the flow rate of oxygen and air can be adjusted during the input process, enabling the first high-frequency generator 301 and the second high-frequency generator 302 to generate high-frequency oscillations. For example, the first high-frequency generator 301 and the second high-frequency generator 302 are each valves that can control the flow rate, thereby controlling the oxygen and air flow rates to generate high-frequency oscillations. To supply air to the patient, in this embodiment, the oxygen input branch 202 and the air input branch 203 merge into a single branch, which is connected to the patient's tubing, thus providing the patient with fresh air and oxygen through this branch.

[0045] Compared to Figure 2 The high-frequency oscillation shown is generated by a first high-frequency generator installed on the oxygen input branch and a second high-frequency generator installed on the air input branch. This embodiment... Figure 3 This provides another way to generate high-frequency oscillations, in Figure 3 The middle inhalation branch also includes an oxygen input branch 202 and an air input branch 203. The oxygen input branch 202 is connected to an oxygen source interface, and oxygen input through the oxygen source interface enters the oxygen input branch 202. The air input branch 203 is connected to an air source interface, and air input through the air source interface enters the air input branch 203.

[0046] and Figure 2The difference is that a first one-way air intake device 204 is provided on the oxygen input branch 202, and a second one-way air intake device 205 is provided on the air input branch 203. The first one-way air intake device 204 controls the flow rate of oxygen input into the oxygen input branch; the second one-way air intake device 205 controls the flow rate of air input into the air input branch. In this way, when oxygen and air are input through the oxygen source interface and the air source interface, there is no need to preset the input ratio of oxygen and air. Instead, the input ratio of oxygen and air and the flow rate of oxygen and air are controlled by the first one-way air intake device 204 and the second one-way air intake device 205. Then, the high-frequency oscillation generator 30 generates high-frequency oscillations from the oxygen input branch and the air input branch.

[0047] In this embodiment, the high-frequency oscillation generator 30 can be installed on the branch where the oxygen input branch 202 and the air input branch 203 converge. This converging branch is connected to the patient tubing, allowing oxygen and air to simultaneously pass through the high-frequency oscillation generator 30 to generate high-frequency oscillations. Under the influence of these high-frequency oscillations, the oxygen and air in the branch are then delivered to the patient through the patient tubing. The high-frequency oscillation generator 30 can be, but is not limited to, a valve capable of controlling the flow rate, such as a proportional solenoid valve or an on / off valve, to generate high-frequency oscillations through flow rate control.

[0048] The controller 40 controls the exhaust device 201 to exhaust the gas exhaled by the patient through the patient tubing at a high frequency when the medical ventilation equipment is in the high-frequency exhalation phase.

[0049] The high-frequency expiratory phase is one of the operating phases of a medical ventilation device. The medical ventilation device includes two operating phases: the high-frequency inhalation phase and the high-frequency expiratory phase. During the high-frequency inhalation phase, oxygen and fresh air are provided to the patient. During the process of the patient inhaling oxygen and fresh air, gases in the patient's body, especially carbon dioxide, are expelled. These gases condense in the breathing circuit. When the medical ventilation device is in the high-frequency expiratory phase, they are expelled at high frequency by the exhaust device 201 set on the breathing circuit, so as to quickly and timely expel the gases in the breathing circuit.

[0050] It's important to clarify that "when the medical ventilation equipment is in the high-frequency expiratory phase" and "when the medical ventilation equipment is in the high-frequency inspiratory phase" do not refer to a specific moment, but rather to the process during which the medical ventilation equipment is in the high-frequency expiratory phase and the high-frequency inspiratory phase, respectively. During the high-frequency inspiratory phase, the equipment continuously supplies air to the patient, while during the high-frequency expiratory phase, the exhaust device 201 actively and continuously exhausts air. When the medical ventilation equipment is in the high-frequency inspiratory phase, the controller 40 can also control the exhaust device 201 to stop exhausting air, preventing a decrease in pressure in the breathing circuit through the exhaust device 201 during the high-frequency inspiratory phase, thus ensuring that oxygen and air can enter the patient's body during this phase.

[0051] In this embodiment, the exhaust device 201 can actively expel gas from the breathing circuit. Since the exhaust device 201 is installed on the breathing circuit, it is not affected by the resistance of the patient's tubing during the exhaust process. This can accelerate the rapid and timely expulsion of gas from the breathing circuit, prevent gas accumulation and increase in the average pressure in the patient's tubing, and ensure the patient's life safety.

[0052] The effects of passive exhaust via patient tubing and active exhaust via exhaust device 201 in this embodiment are explained below with reference to the accompanying drawings:

[0053] Assuming a preset high pressure of 30 cmH2O (hereinafter referred to as cmH2O) and a preset low pressure of 0, the desired target average pressure of 15 cmH2O can ensure patient safety. The gas pressure in the patient's tubing can vary between the preset high and low pressures with the patient's respiration, forming a pressure distribution such as... Figure 4 The airway pressure waveform shown is shown, but the lowest pressure in the patient's tubing is greater than the preset low pressure during the process of venting air through the patient's tubing (e.g., ...). Figure 4 The minimum value of the middle airway pressure waveform is greater than the preset low pressure, resulting in the average pressure in the patient's tubing being greater than the target average pressure. Figure 4 As shown, because the gas in the open circuit cannot be discharged in time, the average pressure in the patient's tubing rises to 22 cmH2O, thereby endangering the patient's life.

[0054] In this embodiment, the active exhaust device 201 will generate the following... Figure 5 The airway pressure waveform shown is from Figure 5 As shown in the airway pressure waveform, during the active air venting process of the venting device 201, the lowest pressure in the patient's tubing is close to the preset low pressure (e.g., equal to, less than, or slightly greater than the preset low pressure at different stages of the air venting process), so that the average pressure in the patient's tubing is close to the target average pressure of 15 cmH2O. This ensures the patient's safety while timely venting the gas from the patient's tubing.

[0055] In addition to medical ventilation devices that exhaust air through open pipelines, there are also medical ventilation devices that exhaust air using a diaphragm method and those that exhaust air using a Venturi jet method. Among them, medical ventilation devices that exhaust air using a diaphragm method require a large-volume closed diaphragm cavity to provide positive and negative pressure. During the process of providing positive and negative pressure in the closed diaphragm cavity, the movement of the closed diaphragm cavity will generate a lot of noise. Medical ventilation devices that exhaust air using a Venturi jet method rely on a high-pressure air source for driving, which consumes a lot of air. However, the medical ventilation device provided in this embodiment, which actively exhausts air using the exhaust device 201, eliminates the need for a closed diaphragm cavity and a high-pressure air source for driving. Therefore, compared with the two existing medical ventilation devices mentioned above, the medical ventilation device in this embodiment has the advantages of small size, low noise, fast response, and low air consumption.

[0056] Please see Figure 6 This illustrates the structure of another medical ventilation device provided by an embodiment of the present invention, in the above... Figure 1 Based on the medical ventilation equipment shown, a data acquisition device 206 is also provided on the breathing circuit 20. The data acquisition device 206 acquires the pressure in the breathing circuit, and the corresponding controller 40 controls the exhaust flow rate of the exhaust device 201 according to the pressure in the breathing circuit 20.

[0057] Specifically, the pressure in the breathing circuit 20 is directly proportional to the exhaust flow rate of the exhaust device 201. The higher the pressure in the breathing circuit 20, the more gas accumulates in the patient's tubing. In this case, the exhaust flow rate of the exhaust device 201 needs to be increased so that the exhaust device 201 discharges more gas per unit time, thereby expelling the gas in the patient's tubing in a timely manner. If the pressure in the breathing circuit 20 is lower, the less gas accumulates in the patient's tubing. In this case, the exhaust flow rate of the exhaust device 201 can be reduced so that the gas discharged by the exhaust device 201 per unit time is reduced, thereby maintaining the gas pressure in the patient's tubing close to the preset low pressure.

[0058] In this embodiment, the exhaust flow rate of the exhaust device 201 can be controlled by, but is not limited to, controlling at least one of the following: the opening duration, opening frequency, and opening angle of the exhaust device 201. It is understood that a larger opening angle indicates a larger opening of the exhaust device 201, resulting in more gas being discharged from the opening of the exhaust device 201 per unit time. The opening duration represents the duration during which the exhaust device 201 is continuously open during the high-frequency exhalation phase of the medical ventilation device; a longer opening duration results in more gas being discharged. If the exhaust device 201 is opened multiple times during the high-frequency exhalation phase, the opening duration represents the duration of a single opening or the sum of the durations of multiple openings; the durations of different openings can be the same or different. The opening frequency represents the number of times the exhaust device 201 is opened during the high-frequency exhalation phase of the medical ventilation device; similarly, a higher opening frequency indicates that the exhaust device 201 is opened more frequently, resulting in more gas being discharged through the exhaust device 201 during the high-frequency exhalation phase.

[0059] During the use of medical ventilation equipment, at least one of the opening duration, opening frequency and opening angle of the exhaust device 201 can be controlled simultaneously, such as controlling the opening duration and opening angle to control the exhaust flow rate. This embodiment will not describe each of these aspects in detail.

[0060] In this embodiment, the controller 40 can control the exhaust flow rate of the exhaust device 201 according to the pressure change in the breathing circuit, so that the exhaust of the exhaust device 201 can change with the pressure change in the breathing circuit, thereby both timely exhausting the gas in the patient's tubing and maintaining the gas pressure in the patient's tubing close to the preset low pressure, ensuring the patient's life safety.

[0061] In this embodiment, the pressure collected by the acquisition device 206 can be, but is not limited to, the pressure generated by the pressure generator 207 installed on the breathing circuit, such as... Figure 7 As shown, the pressure generator 207 can be installed on the side of the breathing circuit close to the patient tubing. The breathing circuit is connected to the gas source interface 10 and the patient tubing 50 connected to the patient's respiratory system. The gas flowing through the patient tubing passes through the pressure generator 207, causing the pressure generator 207 to generate pressure under the action of the gas flowing through the patient tubing. The pressure generated by the pressure generator 207 is collected by the acquisition device 206. The gas flowing through the patient tubing can be the gas delivered to the patient during the high-frequency inspiratory phase of the medical ventilation equipment, and the gas exhaled by the patient during the high-frequency expiratory phase of the medical ventilation equipment. During the high-frequency inspiratory and expiratory phases of the medical ventilation equipment, the pressure generator 207 can generate pressure under the action of the gas.

[0062] Because the pressure generator 207 can be installed on the breathing circuit, especially on the side of the breathing circuit close to the patient tubing, the pressure generated by the pressure generator 207 is close to the pressure in the patient tubing, thereby realizing the control of the exhaust device 201 based on the pressure in the patient tubing.

[0063] It should be noted here that the above-mentioned breathing circuit 20 may also include an expiratory branch. One end of the expiratory branch merges with the inspiratory branch and connects to the patient's tubing, while the other end of the expiratory branch is open to the atmosphere. Figure 8 As shown, the exhaust device 201 is installed on the expiratory branch, and the gas in the patient tubing is discharged to the atmosphere through the exhaust device 201. In addition to the exhaust device 201 being installed on the expiratory branch, the sampling device and pressure generator 207 can be installed at the junction of the expiratory and inspiratory branches, or they can be installed on the patient tubing; this embodiment does not limit this.

[0064] For the aforementioned medical ventilation equipment, an optional structure of the exhaust device 201 in this embodiment is as follows: the exhaust device 201 includes a switching element capable of blocking the breathing circuit and a drive device for controlling the high-frequency opening and closing of the switching element. The switching element capable of blocking the breathing circuit is used to block the connection between the breathing circuit and the atmosphere during the high-frequency inhalation phase of the medical ventilation equipment, thus allowing gas to be delivered to the patient through the breathing circuit. During the high-frequency exhalation phase of the medical ventilation equipment, the switching element connects the breathing circuit to the atmosphere, and gas in the patient tubing connected to the breathing circuit is discharged through the switching element.

[0065] For the drive device, it controls the switch element to open during the high-frequency exhalation phase of the medical ventilation equipment to connect the breathing circuit with the atmosphere; and controls the switch element to close during the high-frequency inhalation phase of the medical ventilation equipment to block the connection between the breathing circuit and the atmosphere.

[0066] The driving device can be a motor that provides power to the switching element. For example, the driving device can be a voice coil motor capable of linear bidirectional motion. The voice coil motor drives the switching element, and because it is capable of linear bidirectional motion, it can output force proportional to the current, quickly controlling the opening and closing of the switching element. When the switching element is open, it connects to the atmosphere; when closed, it blocks the connection. Furthermore, a certain negative pressure is generated at the moment the switching element opens, which can more effectively expel gas without being affected by gas path resistance, tidal volume, or ventilation frequency, ensuring that the average pressure does not increase due to slow gas expulsion caused by these factors.

[0067] In this embodiment, the process by which the controller 40 and the drive device control the switching element is as follows:

[0068] When the medical ventilation equipment is in the high-frequency exhalation phase, the controller 40 sends a drive signal to the drive device based on the pressure in the breathing circuit. The drive device, based on the drive signal, controls at least one of the following: the opening angle, opening frequency, and opening duration of the exhaust port of the switching element. This control of the opening angle, opening frequency, and opening duration enables active exhaust and control of the exhaust flow rate. The opening angle indicates the amount of opening of the exhaust port; a larger opening indicates a larger connection between the breathing circuit and the atmosphere, resulting in a larger exhaust flow rate, while a smaller opening indicates a smaller connection between the breathing circuit and the atmosphere, resulting in a smaller exhaust flow rate. For explanations of the opening frequency and opening duration, please refer to the above description; they will not be repeated here.

[0069] The drive signal sent by the controller 40 can be in the form of a control waveform, enabling the drive device to control the switching element through at least one waveform. The controller 40 generates the control waveform in a manner that is, but not limited to, generating a control waveform for controlling the exhaust device based on the pressure in the breathing circuit. This control waveform is correlated with the pressure in the breathing circuit. Specifically, the control waveform can control at least one of the following: the opening angle, opening frequency, and opening duration of the exhaust port of the switching element, all correlated with the pressure in the breathing circuit. This ensures that the switching element can promptly expel gas and maintain the average pressure in the patient's tubing close to a preset low pressure. The control waveform can be, but is not limited to, any one of the following: sine wave, cosine wave, square wave, triangle wave, exponential function waveform, and Nth power function waveform, where N is greater than or equal to 2.

[0070] In this embodiment, the switching element can be any type of valve capable of blocking the breathing circuit. For example, the switching element can include any of the following: a proportional exhaust valve, a switching valve, and a solenoid valve. The control waveform generated by the controller 40 may differ for different switching elements. This is because although switching valves and solenoid valves have both open and closed modes, the opening angle of their exhaust ports is fixed. Therefore, the control waveform suitable for switching valves and solenoid valves can be a waveform that controls their opening and closing but cannot change their opening angle. Correspondingly, the control waveform for switching valves and solenoid valves can be a square wave. When a square wave is used, the duty cycle of the control waveform is related to the pressure in the breathing circuit. The duty cycle is used to indicate the duration for which the exhaust port of the switching element is open, so that the gas in the patient's tubing can be expelled in a timely manner through the duty cycle related to the pressure in the breathing circuit. For a proportional exhaust valve, the opening angle of its exhaust port is controllable. Therefore, the control waveform corresponding to a proportional exhaust valve is any of the above-mentioned sine wave, cosine wave, square wave, triangular wave, exponential function waveform, and Nth power function waveform, where N is greater than or equal to 2.

[0071] One point to note here is that if the exhaust device 201 is opened rapidly and instantaneously during the high-frequency expiratory phase of the medical ventilation equipment, and the exhaust port of the exhaust device is too large, an excessive negative pressure suction will be generated. This will cause a low-pressure negative overshoot in the patient's tubing, resulting in insufficient amplitude oscillation of the airway pressure waveform in the patient's tubing. Figure 9 As shown. In Figure 9 The central exhaust device 201 quickly opens an excessively large exhaust port, causing the gas in the patient's tubing to be rapidly drawn in, resulting in a low-pressure negative overrush in the patient's tubing. Figure 9 (marked A in the text), which leads to the appearance of Figure 9 The amplitude oscillation indicated by marker B is insufficient.

[0072] To address this issue, the switching element in this embodiment employs a proportional exhaust valve. The corresponding control waveform for this proportional exhaust valve is selected from waveforms with a relatively smooth transition, such as sine waves, cosine waves, exponential function waveforms, and Nth-order function waveforms. This ensures that the opening angle of the exhaust port of the proportional exhaust valve gradually increases, preventing excessive negative pressure suction during smooth opening. For example... Figure 10 As shown, the preferred control waveform for the switching element is... Figure 10 The waveform to the right of the middle arrow, relative to the waveform to the left of the arrow, allows the opening and closing angle of the exhaust port to be gradually increased during the process of controlling the exhaust device 201 using the waveform to the right of the arrow.

[0073] In this embodiment, the exhaust device 201 may further include a turbine negative pressure device, which provides negative pressure suction to the switching element so that the gas in the patient's tubing passes through the switching element and the turbine negative pressure device in sequence for exhaust. During the high-frequency exhalation phase of the medical ventilation device, the turbine negative pressure device generates a negative pressure suction. Under the action of negative pressure suction, the gas in the patient's tubing is drawn out of the exhaust port of the switching element through the breathing circuit, and then discharged into the atmosphere through the cavity of the turbine negative pressure device.

[0074] In addition to being able to exhaust gas through the exhaust device 201, the pressure generator 207 in this embodiment can also exhaust gas when the medical ventilation device is in the high-frequency exhalation stage and / or in the high-frequency inhalation stage, so as to exhaust some gas through the pressure generator 207. In particular, during the high-frequency inhalation stage of the medical ventilation device, the pressure generator 207 exhausts gas to maintain the maximum pressure in the patient's tubing close to the preset high pressure, so as to prevent certain risks caused by excessively high maximum pressure.

[0075] The discharge capacity of a pressure generator is affected by both the type of pressure generator and the type of patient tubing. Different types of pressure generators have different structures, which limit the amount of gas discharged. Therefore, different types of pressure generators may have different discharge port diameters. The size of the discharge port diameter is directly proportional to the discharge capacity; a larger discharge port diameter results in a larger discharge capacity, and a smaller discharge port diameter results in a smaller discharge capacity. Similarly, different types of patient tubing also have different structures. When the same amount of gas is delivered to patient tubing with different structures, the pressure generated will vary. Generally, higher pressure results in a larger discharge volume, and vice versa. Therefore, the type of patient tubing and its corresponding pressure will also affect the discharge capacity of the pressure generator. For example, different types of patient tubing have different pipe diameters, and the pipe diameter is directly proportional to the pressure. Thus, the same amount of gas delivered to patient tubing with different pipe diameters will produce different pressures.

[0076] In this embodiment, the pressure generator discharges gas from the patient's tubing during the high-frequency exhalation phase and / or the high-frequency inhalation phase of the medical ventilation device. This reduces the pressure in the patient's tubing during the high-frequency inhalation phase, bringing the maximum pressure in the patient's tubing close to the preset high pressure, thus preventing certain risks caused by excessively high maximum pressure. During the high-frequency exhalation phase, the exhaust device 201 can assist in exhausting gas, improving exhaust efficiency.

[0077] The above mainly describes the exhaust process of medical ventilation equipment. The following describes the control process of medical ventilation equipment based on mean pressure. The mean pressure of medical ventilation equipment is related to the target amplitude and the respiratory ratio (the ratio of the time spent in expiration to the time spent inspiration). Simultaneously, the mean pressure is also affected by the maximum output capacity of the medical ventilation equipment. If there is excessive leakage at the patient's tubing end or the patient's lung volume is too large, causing the output capacity of the medical ventilation equipment to exceed its maximum output capacity, the medical ventilation equipment will operate at its maximum output capacity. This will cause a deviation between the mean pressure and the target mean pressure. If the mean pressure is less than the target mean pressure or greater than the target mean pressure, the patient's lungs may over-inflate, causing damage. If the mean pressure is less than the target mean pressure, the patient's oxygenation may be insufficient. Therefore, control based on mean pressure is essential, and the control process is as follows:

[0078] In this embodiment, the medical ventilation device may further include: an output capacity acquisition device for acquiring the current output capacity of the medical ventilation device; wherein the current output capacity is used to characterize whether the medical ventilation device is operating at maximum load. For example, the output capacity of the medical ventilation device is represented by the operating current or operating voltage of the medical ventilation device. If the operating current or operating voltage of the medical ventilation device reaches its maximum value, it indicates that the current output capacity of the medical ventilation device has reached its maximum output capacity. Therefore, the output capacity acquisition device may include: an electrical parameter acquisition unit for acquiring the current operating current or operating voltage of the medical ventilation device, wherein the operating current or operating voltage is used to indicate the current output capacity of the medical ventilation device.

[0079] During the high-frequency inhalation phase of a medical ventilation device, the operating current or voltage of the device can be represented by the operating current or voltage generated by the high-frequency oscillation. If the operating current or voltage generated by the high-frequency oscillation reaches its maximum value, it indicates that the current output capacity of the medical ventilation device has reached its maximum output capacity during the high-frequency inhalation phase. During the high-frequency exhalation phase of a medical ventilation device, the operating current or voltage can be represented by the operating current or voltage of the exhaust device. If the operating current or voltage of the exhaust device reaches its maximum value, it indicates that the current output capacity of the medical ventilation device has reached its maximum output capacity during the high-frequency exhalation phase.

[0080] After the output capacity device obtains the current output capacity of the medical ventilation equipment, it sends the current output capacity of the medical ventilation equipment to the controller 40, which then determines whether the current output capacity has reached the maximum output capacity.

[0081] The data acquisition device 206 also acquires the average pressure corresponding to the breathing circuit when the current output capacity of the medical ventilation equipment is the maximum output capacity of the medical ventilation equipment. For example, when the controller 40 determines that the current output capacity has reached the maximum output capacity, it sends an indication signal to the data acquisition device 206 to acquire the average pressure.

[0082] In this embodiment, the acquisition device 206 obtains the average pressure corresponding to the breathing circuit in the following ways: the acquisition device 206 obtains the maximum pressure value and the minimum pressure value corresponding to the breathing circuit, and calculates the average pressure based on the maximum pressure value and the minimum pressure value. During the operation of the medical ventilation equipment, the acquisition device 206 acquires at least one maximum pressure value and at least one minimum pressure value. Based on the at least one maximum pressure value, the acquisition device 206 obtains a maximum target pressure value for calculating the average pressure, such as selecting one maximum pressure value from the maximum pressure values ​​as the maximum target pressure value, or averaging / weighted averaging multiple maximum pressure values ​​to obtain the maximum target pressure value. Similarly, the acquisition device 206 can obtain a minimum target pressure value for calculating the average pressure based on at least one minimum pressure value. The acquisition device 206 calculates the average value of the maximum target pressure value and the minimum target pressure value, and this average value is the average pressure corresponding to the breathing circuit.

[0083] The maximum and minimum pressure values ​​are the actual pressure values ​​during the use of the medical ventilation equipment, while the preset high pressure and preset low pressure are the expected pressure values ​​set during or before the use of the medical ventilation equipment. The actual pressure values ​​may deviate from the expected pressure values.

[0084] The controller 40 also reduces the target amplitude of the medical ventilation device when the average pressure has not reached the target average pressure. The target amplitude is the difference between the preset high pressure corresponding to the breathing circuit during the high-frequency inspiratory phase and the preset low pressure corresponding to the breathing circuit during the high-frequency expiratory phase.

[0085] If the current output capacity of the medical ventilation equipment is at its maximum, but the average pressure has not reached the target average pressure, it indicates that the medical ventilation equipment has failed to ensure that the average pressure matches the target average pressure even at its maximum output capacity. In this case, it is necessary to adjust the target amplitude of the medical ventilation equipment to adjust the target average pressure, so that the average pressure matches the target average pressure when the medical ventilation equipment is at its maximum output capacity, reducing the danger caused by the average pressure being greater than or less than the target average pressure. Specifically, the controller 40 adjusts the target amplitude of the medical ventilation equipment when its current output capacity is at its maximum and the average pressure has not reached the target average pressure as follows:

[0086] If the pressure in the breathing circuit during the high-frequency exhalation phase causes the average pressure to fall short of the target average pressure, the preset low pressure is increased; if the pressure in the breathing circuit during the high-frequency inhalation phase causes the average pressure to fall short of the target average pressure, the preset high pressure is decreased.

[0087] It is understandable that the average pressure not reaching the target average pressure may be due to the preset low pressure being too low or the preset high pressure being too high. Therefore, the controller 40 needs to first determine whether the average pressure is not reaching the target average pressure due to the preset low pressure or the preset high pressure, and then adjust the preset low pressure or the preset high pressure to achieve the adjustment of the target amplitude. Specifically, if the pressure in the breathing circuit during the high-frequency exhalation phase causes the average pressure to not reach the target average pressure, it indicates that there is too much gas in the patient's tubing, causing the exhaust device 201 to actively exhaust the gas and fail to reduce the pressure in the patient's tubing to the preset low pressure, or that the preset low pressure is too low. In this case, the controller 40 can increase the preset low pressure. If the pressure in the breathing circuit during the high-frequency inhalation phase causes the average pressure to not reach the target average pressure, it indicates that there is insufficient gas delivered to the breathing circuit or that the preset high pressure is too high. In this case, the controller 40 can decrease the preset high pressure.

[0088] After the controller 40 reduces the target amplitude, the controller 40 can further continuously monitor whether the average pressure reaches the target average pressure. If the average pressure does not reach the target average pressure within a preset time after reducing the target amplitude of the medical ventilation device, it indicates that the medical ventilation device may be faulty. Therefore, it is necessary to output a prompt message. Correspondingly, the medical ventilation device in this embodiment also includes: a prompting device; the controller 40 is used to control the prompting device to output a prompt message if the average pressure does not reach the target average pressure within a preset time after reducing the target amplitude of the medical ventilation device. The prompt message is used to indicate that the medical ventilation device is faulty and needs to be manually checked.

[0089] If the current output capacity of the medical ventilation device is the maximum output capacity but the average pressure reaches the target average pressure, it means that the medical ventilation device can maintain the preset low pressure and preset high pressure. The controller 40 can then control the breathing circuit with the target amplitude. Alternatively, if the current output capacity of the medical ventilation device does not reach the maximum output capacity, the controller 40 can also control the breathing circuit with the target amplitude. In other words, if the current output capacity of the medical ventilation device does not reach the maximum output capacity, even if the average pressure does not reach the target average pressure, the controller 40 can increase the output capacity of the medical ventilation device to make the average pressure reach the target average pressure. Therefore, in this case, the controller 40 can continue to control the breathing circuit with the target amplitude.

[0090] By controlling the target amplitude based on the average pressure and the current output capacity of the medical ventilation equipment, the average pressure of the medical ventilation equipment is made consistent with the target average pressure, thereby reducing the danger caused by the inconsistency between the average pressure and the target average pressure.

[0091] In this embodiment, the medical ventilation device can also control various devices in the breathing circuit. The corresponding medical ventilation device also includes: a working parameter acquisition device, which acquires and sets the working parameters of various devices in the air source interface and breathing circuit, such as the working parameters of the exhaust device, pressure generator, etc. The working parameters of any device are used to indicate the current load of the device. For example, the working parameters of any device can be the working current or working voltage of the device, so as to determine whether it is working under the maximum load by the working current or working voltage. For details, please refer to the description of the output capacity acquisition device mentioned above, which will not be described in detail here.

[0092] The acquisition device 206 also acquires the pressure in the breathing circuit during the high-frequency oscillation process; the controller 40 also obtains the pressure amplitude corresponding to the breathing circuit based on the pressure in the breathing circuit. The pressure amplitude is the pressure difference between the maximum and minimum pressure values ​​in the breathing circuit, as described above. Figure 5 The diagram shows the amplitude (actual amplitude) of the airway pressure waveform. If the pressure amplitude corresponding to the breathing circuit does not reach the target amplitude, the controller 40 adjusts the operating parameters of each device. The target amplitude is the difference between the preset high pressure corresponding to the breathing circuit during the high-frequency inhalation phase and the preset low pressure corresponding to the breathing circuit during the high-frequency exhalation phase (i.e., the desired amplitude).

[0093] If the pressure amplitude corresponding to the breathing circuit does not reach the target amplitude, it means that at least one of the maximum and minimum pressure values ​​corresponding to the breathing circuit has not reached the preset pressure. For example, if the maximum pressure value does not reach the preset high pressure and / or the minimum pressure value does not reach the preset low pressure, the controller 40 needs to adjust the operating parameters of each device to make the pressure amplitude reach the target amplitude. The adjustment process includes, but is not limited to, the following methods:

[0094] If the pressure amplitude corresponding to the breathing circuit does not reach the target amplitude, the controller 40 obtains the compensation parameters of the working parameters of each device based on the difference between the pressure amplitude corresponding to the breathing circuit and the target amplitude. The compensation parameters of the working parameters of each device are used to adjust the working parameters of each device. The compensation parameters have a one-to-one relationship with the device, so that the working parameters of the device can be adjusted by the compensation parameters of any device, such as reducing or increasing the working parameters of the device by the compensation parameters of the device.

[0095] For example, if the pressure amplitude corresponding to the breathing circuit is less than the target amplitude, the pressure amplitude corresponding to the breathing circuit can be increased. One way to increase the pressure amplitude is to obtain compensation parameters for increasing high-frequency oscillations. Increasing high-frequency oscillations means increasing the oscillation amplitude of the gas in the patient's tubing to increase the pressure amplitude corresponding to the breathing circuit. If the pressure amplitude is less than the target amplitude because the low pressure is less than the preset low pressure, the operating parameters of the device used for exhaust can be increased to increase the exhaust flow rate. For example, increasing the operating parameters of the exhaust device increases the exhaust flow rate per unit time. If the pressure amplitude is less than the target amplitude because the high pressure is less than the preset high pressure, the operating parameters of the device used for intake can be increased to increase the intake flow rate. For example, increasing the operating parameters of the high-frequency oscillation generating device can increase the intake flow rate. If the breathing circuit... If the pressure amplitude corresponding to the breathing circuit is greater than the target amplitude, the pressure amplitude corresponding to the breathing circuit is reduced. One way to reduce the pressure amplitude corresponding to the breathing circuit is to obtain compensation parameters to reduce high-frequency oscillations if the pressure amplitude corresponding to the breathing circuit is greater than the target amplitude. Reducing high-frequency oscillations means reducing the oscillation amplitude of the gas in the patient's tubing to reduce the pressure amplitude corresponding to the breathing circuit. Similarly, if the pressure amplitude is greater than the target amplitude because the low pressure is less than the preset low pressure, the operating parameters of the device used for exhaust can be reduced to reduce the exhaust flow rate. For example, reducing the operating parameters of the exhaust device reduces the exhaust flow rate per unit time. If the pressure amplitude is greater than the target amplitude because the high pressure is greater than the preset high pressure, the operating parameters of the device used for intake can be reduced to reduce the intake flow rate. For example, reducing the operating parameters of the high-frequency oscillation generating device.

[0096] If the pressure amplitude corresponding to the breathing circuit reaches the target amplitude, the controller 40 maintains the operating parameters of each device. If the pressure amplitude corresponding to the breathing circuit reaches the target amplitude, it means that the operating parameters of each device in the breathing circuit can meet the requirements of the preset low pressure and preset high pressure. Then the controller 40 can continue to use the current operating parameters of each device to control each device.

[0097] It should be noted that the above description only covers some of the devices in medical ventilation equipment. In addition to the devices mentioned above, medical ventilation equipment also includes other devices, such as... Figure 11 and Figure 12 As shown, each of these illustrates an optional structure of another medical ventilation device provided by an embodiment of the present invention:

[0098] like Figure 11As shown, the oxygen source interface is used to connect to an oxygen source. The oxygen source passes through filter 3 to prevent impurities from flowing downstream of the oxygen input branch, protecting the devices located downstream of the oxygen input branch. Pressure sensor 4 monitors the pressure of the oxygen source interface and can trigger an alarm based on a set value when the pressure of the oxygen source interface is too high or too low. One-way valve 5 prevents reverse flow of oxygen in the oxygen input branch and can also control the oxygen flow rate. Pressure regulating valve 6 is used to stabilize the pressure of the oxygen input through the oxygen source interface, ensuring accurate control of downstream flow and pressure. Flow regulating valve 7, as the first high-frequency generating device 301, is used to regulate and control the oxygen flow rate. Filter 8 further purifies the input oxygen, protecting the downstream flow sensor 9 for accurate measurement of oxygen flow and, in some cases, also stabilizing the flow rate. The air source interface is used to connect to an air source. The air source passes through filter 11 to prevent impurities from flowing downstream of the air input branch, protecting the devices located downstream of the air input branch. Pressure sensor 12 monitors the pressure of the air source interface and can trigger an alarm based on a set value when the pressure is too high or too low. One-way valve 13 prevents reverse airflow in the air input branch and also controls the air flow rate. Pressure regulating valve 14 stabilizes the pressure of the air input at the air source interface, ensuring accurate control of downstream flow and pressure. Flow regulating valve 15, as the second high-frequency generator 302, regulates and controls the air flow rate. Filter 16 further purifies the input air, protecting the downstream flow sensor 17's accurate measurement of air flow rate, and in some cases, also helps stabilize the flow rate. Flow regulating valve 7, as the first high-frequency generator 301, and flow regulating valve 15, as the second high-frequency generator 302, respectively control the flow rates of oxygen and air, thereby controlling the oxygen concentration in the mixed gas and generating high-frequency oscillations to deliver oxygen and fresh air to the patient's tubing. Flow regulating valves 7 and 15 can be proportional solenoid valves, shut-off valves, on / off valves, or other servo valves capable of adjusting flow rates, all achieving the purpose of delivering gas to the patient's tubing. One-way valve 19 prevents exhaled air from entering the oxygen and air input branches during the patient's exhalation (i.e., during the high-frequency exhalation phase). Safety valve 20 opens to allow air to the atmosphere when the pressure in the breathing circuit reaches its maximum set value, thus releasing pressure and preventing danger due to excessive pressure. Additionally, if insufficient inhaled air is supplied to the front of safety valve 20, it switches to atmospheric flow, allowing the patient to inhale air from the atmosphere. Humidifier 21 heats and humidifies the inhaled air, ensuring the temperature and humidity of the inhaled air and the patient's comfort. Pressure generator 25 (corresponding to pressure generator 207) generates pressure, allowing some air to enter the patient's body while the rest is expelled through pressure generator 25. The patient's airway pressure is monitored by proximal pressure sensor 24.During the high-frequency inhalation phase, the flow regulating valve 7 (as the first high-frequency generating device 301) and the flow regulating valve 15 (as the second high-frequency generating device 302) control the flow rate to increase and generate high pressure. Meanwhile, the proportional exhaust valve 22 (as the exhaust device 201) is in a flow-limiting state to prevent pressure drop. During the high-frequency exhalation phase, the flow regulating valve 7 (as the first high-frequency generating device 301) and the flow regulating valve 15 (as the second high-frequency generating device 302) control the flow rate to decrease rapidly. Simultaneously, the proportional exhaust valve 22 performs active exhaust control to release pressure. This cyclical control achieves a high-frequency oscillation effect.

[0099] Compared to Figure 11 The medical ventilation equipment shown is... Figure 12 The differences between the medical ventilation devices shown are: Figure 12 The illustrated medical ventilation device omits pressure regulating valves 6 and 14, and adds a flow regulating valve 18 to save costs. High-frequency oscillations are generated via flow regulating valve 18, while flow regulating valves 7 and 15 are only used for flow regulation. Furthermore, in the medical ventilation device that omits pressure regulating valves 6 and 14, the input ratio of oxygen and air needs to be set before delivering gas to the oxygen source interface and air source interface.

[0100] This invention also provides a control method for a medical ventilation device, wherein the medical ventilation device includes an air source interface, a breathing circuit, a high-frequency oscillation generator, and a controller. The breathing circuit is equipped with an exhaust device and is connected to the air source interface and a patient tubing connected to the patient's respiratory system. For details, please refer to the above-described device embodiment, which will not be elaborated here.

[0101] The controller in the medical ventilation equipment executes the control method of the medical ventilation equipment. The flowchart of the control method of the medical ventilation equipment is as follows: Figure 13 As shown, the following steps may be included:

[0102] 501: A high-frequency oscillation generator is used to generate high-frequency oscillations in the inspiratory branch of the breathing circuit. The methods by which the inspiratory branch and the high-frequency oscillation generator generate high-frequency oscillations include, but are not limited to, the following:

[0103] One approach: The inspiratory circuit includes an oxygen input branch and an air input branch, and the high-frequency oscillation generating device includes a first high-frequency generating device and a second high-frequency generating device. The first high-frequency generating device is installed on the oxygen input branch, and the second high-frequency generating device is installed on the air input branch. Correspondingly, generating high-frequency oscillations in the gas of the inspiratory branch of the breathing circuit through the high-frequency oscillation generating device involves: using the first and second high-frequency generating devices, when the medical ventilation device is in the high-frequency inspiratory phase, generating high-frequency oscillations in the oxygen in the oxygen input branch and the air in the air input branch.

[0104] Another approach: The inspiratory branch includes an oxygen input branch and an air input branch. A first one-way air intake device is installed on the oxygen input branch, and a second one-way air intake device is installed on the air input branch. Correspondingly, the control method for the medical ventilation equipment also includes: controlling the flow rate of oxygen input to the oxygen input branch through the first one-way air intake device, and controlling the flow rate of air input to the air input branch through the second one-way air intake device. Then, generating high-frequency oscillations in the gas of the inspiratory branch of the breathing circuit using a high-frequency oscillation generator includes: generating high-frequency oscillations between the oxygen input branch and the air input branch using the high-frequency oscillation generator.

[0105] For an explanation of the high-frequency oscillation generation device and the intake branch, please refer to the relevant descriptions in the above device embodiments, which will not be elaborated here.

[0106] 502: When the medical ventilation equipment is in the high-frequency exhalation phase, the exhaust device is controlled to expel the gas exhaled by the patient through the patient tubing at a high frequency.

[0107] In this embodiment, the exhaust device includes a switching element capable of blocking the breathing circuit and a drive device for controlling the high-frequency opening and closing of the switching element. The switching element includes a proportional exhaust valve, a switching valve, or a solenoid valve. The methods for controlling the high-frequency exhaust device to expel gas exhaled by the patient through the patient's tubing include, but are not limited to:

[0108] When the medical ventilation equipment is in the high-frequency exhalation phase, a drive signal is sent to the drive device based on the pressure in the breathing circuit. The drive device then controls at least one of the following: the opening angle, opening frequency, and opening duration of the exhaust port of the switching element, according to the drive signal, to achieve high-frequency gas expulsion. The drive signal can be a control waveform, which is generated based on the pressure in the breathing circuit to control the exhaust device. For example, the control waveform can be any one of a sine wave, cosine wave, square wave, triangular wave, exponential function waveform, and Nth-order function waveform, where N is greater than or equal to 2. When the control waveform is a square wave, the duty cycle of the control waveform is related to the pressure in the breathing circuit.

[0109] In addition, the exhaust device also includes a turbine negative pressure device, and the corresponding high-frequency exhaust control device also includes: providing negative pressure suction to the switching element through the turbine negative pressure device, so that the gas in the patient's tubing passes through the switching element and the turbine negative pressure device in sequence and is discharged.

[0110] For a description of the high-frequency exhaust and the structure of the exhaust device, please refer to the above-described equipment embodiment; further details will not be repeated here.

[0111] In this embodiment, the exhaust device actively expels gas from the breathing circuit. The exhaust device is located on the breathing circuit so that it is not affected by the resistance of the patient's tubing during the exhaust process. This can accelerate the rapid and timely expulsion of gas from the breathing circuit, prevent gas accumulation and increase in the average pressure in the patient's tubing, and ensure the patient's safety.

[0112] Please see Figure 14 It illustrates a flowchart of another control method for a medical ventilation device provided by an embodiment of the present invention, in the above... Figure 13 In addition, the following steps can be included:

[0113] 503: The pressure in the breathing circuit is collected by a sampling device on the breathing circuit. The pressure in the breathing circuit is generated by a pressure generator installed on the breathing circuit. The pressure generator generates pressure under the action of gas flowing through the patient's tubing.

[0114] 504: Control the exhaust flow rate of the exhaust device based on the pressure in the breathing circuit. Specifically, the pressure in the breathing circuit is directly proportional to the exhaust flow rate of the exhaust device. The higher the pressure in the breathing circuit, the more gas has accumulated in the patient's tubing. In this case, the exhaust flow rate of the exhaust device needs to be increased so that more gas is expelled per unit time, thereby expelling the gas in the patient's tubing in a timely manner. Conversely, the lower the pressure in the breathing circuit, the less gas has accumulated in the patient's tubing. In this case, the exhaust flow rate of the exhaust device can be reduced so that less gas is expelled per unit time, thereby maintaining the gas pressure in the patient's tubing close to the preset low pressure.

[0115] In this embodiment, the way to control the exhaust flow of the exhaust device may be, but is not limited to, controlling at least one of the opening duration, opening frequency and opening angle of the exhaust device, as described above.

[0116] In this embodiment, the controller can control the exhaust flow rate of the exhaust device according to the pressure change in the breathing circuit, so that the exhaust of the exhaust device can change with the pressure change in the breathing circuit. This can both timely expel the gas in the patient's tubing and maintain the gas pressure in the patient's tubing close to the preset low pressure, thus ensuring the patient's life safety.

[0117] In this embodiment, the control method for the medical ventilation device can further include: controlling the exhaust device to stop exhausting when the medical ventilation device is in the high-frequency inspiratory phase, to prevent the pressure from being too low during the high-frequency inspiratory phase, which could prevent gas from being delivered to the patient in a timely manner. Furthermore, the control method for the medical ventilation device can also include: exhausting gas through a pressure generator when the medical ventilation device is in the high-frequency expiratory phase and / or in the high-frequency inspiratory phase. The type of pressure generator and the type of patient tubing affect the exhaust volume of the pressure generator. By using the pressure generator to exhaust gas from the patient tubing during the high-frequency expiratory phase and / or inspiratory phase, the pressure in the patient tubing can be reduced during the high-frequency inspiratory phase, bringing the maximum pressure in the patient tubing close to the preset high pressure, preventing risks caused by excessively high maximum pressure. During the high-frequency expiratory phase, the exhaust device 201 can assist in exhausting gas, improving exhaust efficiency.

[0118] Please see Figure 15 It shows a flowchart of a control method for another medical ventilation device provided in an embodiment of the present invention. Figure 13 or Figure 14 Furthermore, control can be implemented based on average pressure. Figure 15 Is Figure 13 Add the following steps to the basics:

[0119] 505: Obtain the current output capacity of the medical ventilation equipment. The current operating current or voltage of the medical ventilation equipment indicates its current output capacity.

[0120] 506: When the current output capacity of the medical ventilation equipment is the maximum output capacity of the medical ventilation equipment, obtain the average pressure corresponding to the breathing circuit.

[0121] 507: When the mean pressure does not reach the target mean pressure, reduce the target amplitude of the medical ventilation device. The target amplitude is the difference between the preset high pressure corresponding to the breathing circuit during the high-frequency inspiratory phase and the preset low pressure corresponding to the breathing circuit during the high-frequency expiratory phase. The methods for reducing the target amplitude of the medical ventilation device when the mean pressure does not reach the target mean pressure include, but are not limited to, the following:

[0122] If the pressure in the breathing circuit during the high-frequency exhalation phase causes the average pressure to fall short of the target average pressure, the preset low pressure is increased; if the pressure in the breathing circuit during the high-frequency inhalation phase causes the average pressure to fall short of the target average pressure, the preset high pressure is decreased. For specific adjustment instructions, please refer to the relevant descriptions in the above device embodiments.

[0123] If the average pressure fails to reach the target average pressure within a preset time after reducing the target amplitude, the control method for the medical ventilation equipment provided in this embodiment can also control the prompting device in the medical ventilation equipment to output prompting information.

[0124] If the average pressure reaches the target average pressure, the control method for the medical ventilation device provided in this embodiment can also control the breathing circuit with the target amplitude; or if the current output capacity of the medical ventilation device does not reach the maximum output capacity of the medical ventilation device, the control method for the medical ventilation device provided in this embodiment can also control the breathing circuit with the target amplitude.

[0125] Please see Figure 16 It shows a flowchart of a control method for another medical ventilation device provided in an embodiment of the present invention. Figures 13 to 15 Furthermore, control can be implemented based on average pressure. Figure 16 Is Figure 15 Add the following steps to the basics:

[0126] 508: Obtain the operating parameters of each device set in the air source interface and breathing circuit. The operating parameters of any device are used to indicate the current load of the device. For example, the operating parameters of any device can be the operating current or operating voltage of the device, so as to determine whether it is operating under the maximum load by the operating current or operating voltage. For details, please refer to the description of the output capacity acquisition device mentioned above, which will not be elaborated here.

[0127] 509: Acquire pressure in the breathing circuit during the formation of high-frequency oscillations.

[0128] 510: The pressure amplitude corresponding to the breathing circuit is obtained based on the pressure in the breathing circuit. The pressure amplitude is the pressure difference between the maximum and minimum pressure values ​​in the breathing circuit, as described above. Figure 5 The amplitude (actual amplitude) of the airway pressure waveform shown in the schematic diagram is corresponding to the effect.

[0129] 511: If the pressure amplitude corresponding to the breathing circuit does not reach the target amplitude, the operating parameters of each device are adjusted. The target amplitude is the difference between the preset high pressure corresponding to the breathing circuit during the high-frequency inhalation phase and the preset low pressure corresponding to the breathing circuit during the high-frequency exhalation phase. In this embodiment, the methods for adjusting the operating parameters of each device include, but are not limited to, the following:

[0130] If the pressure amplitude corresponding to the breathing circuit does not reach the target amplitude, the compensation parameters of the working parameters of each device are obtained based on the difference between the pressure amplitude corresponding to the breathing circuit and the target amplitude. The compensation parameters of the working parameters of each device are used to adjust the working parameters of each device. The compensation parameters have a one-to-one relationship with the device, so that the working parameters of the device can be adjusted by the compensation parameters of any device, such as reducing or increasing the working parameters of the device by the compensation parameters of the device.

[0131] In this embodiment, the process of obtaining the compensation parameters for the operating parameters of each device is as follows:

[0132] If the pressure amplitude corresponding to the breathing circuit is less than the target amplitude, the pressure amplitude corresponding to the breathing circuit is increased. One way to do this is to obtain compensation parameters for increasing high-frequency oscillations if the pressure amplitude corresponding to the breathing circuit is less than the target amplitude. If the pressure amplitude corresponding to the breathing circuit is greater than the target amplitude, the pressure amplitude corresponding to the breathing circuit is decreased. Another way to do this is to obtain compensation parameters for decreasing high-frequency oscillations if the pressure amplitude corresponding to the breathing circuit is greater than the target amplitude. For details, please refer to the above device embodiment, which will not be elaborated here.

[0133] Regarding the control method for the aforementioned medical ventilation equipment, the control method for the medical ventilation equipment provided in this embodiment may further include: maintaining the operating parameters of each device if the pressure amplitude corresponding to the breathing circuit reaches the target amplitude.

[0134] In addition, this embodiment also provides a computer-readable storage medium storing executable instructions, configured to cause a processor to execute the executable instructions to implement the above-mentioned control method for medical ventilation equipment.

[0135] Those skilled in the art will understand that embodiments of the present invention can be provided as methods, systems, or computer program products. Therefore, embodiments of the present invention can take the form of hardware embodiments, software embodiments, or embodiments combining software and hardware aspects. Furthermore, embodiments of the present invention can take the form of a computer program product implemented on one or more computer-usable storage media (including disk storage and optical storage, etc.) containing computer-usable program code.

[0136] Embodiments of the present invention are described with reference to flowchart illustrations and / or block diagrams of methods, apparatus (systems), and computer program products according to embodiments of the invention. It will be understood that each block of the flowchart illustrations and / or block diagrams, and combinations of blocks in the flowchart illustrations and / or block diagrams, can be implemented by computer program operations. These computer programs can be provided to operate on a processor of a general-purpose computer, special-purpose computer, embedded processor, or other programmable data processing device to produce a machine, such that operations performed by the processor of the computer or other programmable data processing device produce implementations in the flowchart. Figure 1 One or more processes and / or boxes Figure 1 A device that provides the functions specified in one or more boxes.

[0137] These computer program operations may also be stored in a computer-readable storage medium that can direct a computer or other programmable data processing device to operate in a particular manner, such that the operations stored in the computer-readable storage medium produce an article of manufacture including an operating device, the operating device being implemented in a process Figure 1 One or more processes and / or boxes Figure 1 The function specified in one or more boxes.

[0138] These computer program operations can also be loaded onto a computer or other programmable data processing equipment, causing a series of operational steps to be performed on the computer or other programmable equipment to produce a computer-implemented process, thereby providing the operations performed on the computer or other programmable equipment for implementing the process. Figure 1 One or more processes and / or boxes Figure 1 The steps of the function specified in one or more boxes.

[0139] The above description is merely a preferred embodiment of the present invention and is not intended to limit the scope of protection of the present invention. Any modifications, equivalent substitutions, and improvements made within the spirit and principles of the present invention should be included within the scope of protection of the present invention.

Claims

1. A medical ventilation device, the medical ventilation device comprising an air source interface, a breathing circuit, a high-frequency oscillation generator and a controller, wherein an exhaust device is provided on the breathing circuit; The breathing circuit is connected to the gas source interface and the patient tubing connected to the patient's respiratory system, and the breathing circuit includes an inspiratory branch. The high-frequency oscillation generating device generates high-frequency oscillations in the gas of the intake branch; The controller controls the exhaust device to expel the gas exhaled by the patient through the patient tubing at a high frequency when the medical ventilation device is in the high-frequency exhalation phase. wherein The medical ventilation equipment also includes: Output capacity acquisition device, acquires the current output capacity of the medical ventilation equipment; The data acquisition device collects the pressure in the breathing circuit and obtains the average pressure corresponding to the breathing circuit when the current output capacity of the medical ventilation device is the maximum output capacity of the medical ventilation device. The controller also reduces the target amplitude of the medical ventilation device when the average pressure does not reach the target average pressure. The target amplitude is the difference between the preset high pressure corresponding to the breathing circuit during the high-frequency inhalation phase and the preset low pressure corresponding to the breathing circuit during the high-frequency exhalation phase.

2. The medical ventilation device according to claim 1, wherein the controller is further configured to control the exhaust flow rate of the exhaust device according to the pressure in the breathing circuit.

3. The medical ventilation device of claim 1, wherein, The breathing circuit is also equipped with a pressure generator, which generates pressure under the action of gas flowing through the patient tubing; the acquisition device acquires the pressure in the breathing circuit by acquiring the pressure generated by the pressure generator.

4. The medical ventilation device of claim 1, wherein, The controller also controls the exhaust device to stop exhausting when the medical ventilation device is in the high-frequency inhalation phase.

5. The medical ventilation device of claim 1, wherein, The exhaust device includes a switching element that can block the breathing circuit and a drive device that controls the high-frequency opening and closing of the switching element.

6. The medical ventilation device according to claim 5, wherein, When the medical ventilation device is in the high-frequency exhalation phase, the controller generates a control waveform as a drive signal to control the exhaust device based on the pressure in the breathing circuit, and sends the drive signal to the drive device; the control waveform is correlated with the pressure in the breathing circuit. The drive device controls at least one of the opening angle, opening frequency, and opening duration of the exhaust port of the switching element according to the drive signal, so that at least one of the opening angle, opening frequency, and opening duration of the exhaust port of the switching element is associated with the pressure in the breathing circuit.

7. The medical ventilation device according to claim 5, wherein, The switching element includes a proportional exhaust valve; the control waveform generated by the controller corresponding to the proportional exhaust valve is selected from one or more of sine wave, cosine wave, exponential function waveform and Nth power function waveform, where N is greater than or equal to 2.

8. The medical ventilation device according to claim 7, wherein, The duty cycle of the control waveform is related to the pressure in the breathing circuit.

9. The medical ventilation device according to claim 5, wherein, The exhaust device also includes a turbine negative pressure device, which provides negative pressure to the switching element so that the gas in the patient's tubing passes through the switching element and the turbine negative pressure device in sequence and is then discharged.

10. The medical ventilation device according to claim 3, wherein, The pressure generator also exhausts air when the medical ventilation device is in the high-frequency expiratory phase and / or in the high-frequency inspiratory phase.

11. The medical ventilation device according to claim 1, wherein, The intake branch includes an oxygen input branch and an air input branch, and the high-frequency oscillation generating device includes a first high-frequency generating device and a second high-frequency generating device; the first high-frequency generating device is provided on the oxygen input branch, and the second high-frequency generating device is provided on the air input branch. The first high-frequency generating device and the second high-frequency generating device generate high-frequency oscillations by combining oxygen in the oxygen input branch and air in the air input branch when the medical ventilation device is in the high-frequency inhalation phase.

12. The medical ventilation device according to claim 1, wherein, The intake branch includes an oxygen input branch and an air input branch. A first one-way air intake device is provided on the oxygen input branch, and a second one-way air intake device is provided on the air input branch. The first one-way air intake device controls the flow rate of oxygen input into the oxygen input branch; The second one-way air intake device controls the flow rate of air input into the air input branch; The high-frequency oscillation generating device generates high-frequency oscillations between the oxygen input in the oxygen input branch and the air input in the air input branch.

13. The medical ventilation device according to claim 12, wherein, The controller is configured to increase the preset low pressure if the pressure in the breathing circuit during the high-frequency exhalation phase causes the average pressure to fail to reach the target average pressure. And to reduce the preset high pressure if the pressure in the breathing circuit during the high-frequency inhalation phase causes the average pressure to fail to reach the target average pressure.

14. The medical ventilation device according to claim 1, wherein, The medical ventilation equipment also includes: a prompting device; The controller is further configured to control the prompting device to output a prompt message if the average pressure fails to reach the target average pressure within a preset time after the target amplitude of the medical ventilation device is reduced.

15. The medical ventilation device according to claim 1, wherein, The controller is further configured to control the breathing circuit with the target amplitude if the average pressure reaches the target average pressure; or The controller is further configured to control the breathing circuit with the target amplitude if the current output capacity of the medical ventilation device does not reach the maximum output capacity of the medical ventilation device.

16. The medical ventilation device according to claim 1, wherein, The output capability acquisition device includes an electrical parameter acquisition unit, which acquires the current operating current or operating voltage of the medical ventilation device. The operating current or operating voltage is used to indicate the current output capability of the medical ventilation device.

17. The medical ventilation device according to claim 1, wherein, The medical ventilation device further includes: a working parameter acquisition device, which acquires the working parameters of each device set in the air source interface and the breathing circuit; The acquisition device also acquires the pressure in the breathing circuit during the formation of the high-frequency oscillation; The controller also obtains the pressure amplitude corresponding to the breathing circuit based on the pressure in the breathing circuit. If the pressure amplitude corresponding to the breathing circuit does not reach the target amplitude, the operating parameters of each device are adjusted. The target amplitude is the difference between the preset high pressure corresponding to the breathing circuit during the high-frequency inhalation stage and the preset low pressure corresponding to the breathing circuit during the high-frequency exhalation stage.

18. The medical ventilation device according to claim 17, wherein, The controller is configured to, if the pressure amplitude corresponding to the breathing circuit does not reach the target amplitude, obtain compensation parameters for the operating parameters of each device based on the difference between the pressure amplitude corresponding to the breathing circuit and the target amplitude, and the compensation parameters for the operating parameters of each device are used to adjust the operating parameters of each device.

19. The medical ventilation device according to claim 18, wherein, The controller is configured to increase the pressure amplitude corresponding to the breathing circuit if the pressure amplitude corresponding to the breathing circuit is less than the target amplitude; and to decrease the pressure amplitude corresponding to the breathing circuit if the pressure amplitude corresponding to the breathing circuit is greater than the target amplitude.

20. A control method for a medical ventilation device, the medical ventilation device comprising an air source interface, a breathing circuit, a high-frequency oscillation generator, and a controller, wherein the breathing circuit is provided with an exhaust device, the breathing circuit is respectively connected to the air source interface and a patient tubing connected to a patient's respiratory system, wherein the controller executes the control method, the control method comprising: The high-frequency oscillation generating device generates high-frequency oscillations in the inspiratory branch of the breathing circuit. When the medical ventilation device is in the high-frequency exhalation phase, the exhaust device is controlled to expel the gas exhaled by the patient through the patient tubing at a high frequency; The method further includes: Obtain the current output capacity of the medical ventilation device; The pressure in the breathing circuit is collected, and when the current output capacity of the medical ventilation device is the maximum output capacity of the medical ventilation device, the average pressure corresponding to the breathing circuit is obtained; When the average pressure does not reach the target average pressure, the target amplitude of the medical ventilation device is reduced. The target amplitude is the difference between the preset high pressure corresponding to the breathing circuit during the high-frequency inhalation phase and the preset low pressure corresponding to the breathing circuit during the high-frequency exhalation phase.

21. The control method according to claim 20, wherein, The method further includes: The exhaust flow rate of the exhaust device is controlled according to the pressure in the breathing circuit.

22. The control method according to claim 20, wherein, The pressure in the breathing circuit is generated by a pressure generator installed on the breathing circuit, which generates pressure under the action of gas flowing through the patient tubing.

23. The control method according to claim 20, wherein, The method further includes: When the medical ventilation device is in the high-frequency inhalation phase, the exhaust device is controlled to stop exhausting.

24. The control method according to claim 20, wherein, The exhaust device includes a switching element that can block the breathing circuit and a drive device that controls the high-frequency opening and closing of the switching element.

25. The control method according to claim 24, wherein, When the medical ventilation device is in the high-frequency exhalation phase, controlling the exhaust device to expel the gas exhaled by the patient through the patient tubing at a high frequency includes: When the medical ventilation device is in the high-frequency exhalation phase, a control waveform for controlling the exhaust device is generated as a drive signal based on the pressure in the breathing circuit, and a drive signal is sent to the drive device; the control waveform is correlated with the pressure in the breathing circuit. The driving device controls at least one of the opening angle, opening frequency, and opening duration of the exhaust port of the switching element according to the driving signal, so that at least one of the opening angle, opening frequency, and opening duration of the exhaust port of the switching element is associated with the pressure in the breathing circuit.

26. The control method according to claim 24, wherein, The switching element includes a proportional exhaust valve; the control waveform generated by the controller corresponding to the proportional exhaust valve is selected from one or more of sine wave, cosine wave, exponential function waveform and Nth power function waveform, where N is greater than or equal to 2.

27. The control method according to claim 26, wherein, The duty cycle of the control waveform is related to the pressure in the breathing circuit.

28. The control method according to claim 24, wherein, The exhaust device further includes a turbine negative pressure device, and the step of controlling the exhaust device to discharge the gas exhaled by the patient through the patient tubing at a high frequency when the medical ventilation equipment is in the high-frequency exhalation phase further includes: The turbine negative pressure device provides negative pressure suction to the switching element, so that the gas in the patient's tubing passes through the switching element and the turbine negative pressure device in sequence and is discharged.

29. The control method according to claim 22, wherein, The method further includes: Exhaust is vented through the pressure generator during the high-frequency expiratory phase and / or the high-frequency inspiratory phase of the medical ventilation device.

30. The control method according to claim 20, wherein, The intake branch includes an oxygen input branch and an air input branch, and the high-frequency oscillation generating device includes a first high-frequency generating device and a second high-frequency generating device; the first high-frequency generating device is provided on the oxygen input branch, and the second high-frequency generating device is provided on the air input branch. The step of generating high-frequency oscillations in the inspiratory branch of the breathing circuit using a high-frequency oscillation generating device includes: generating high-frequency oscillations by using the first high-frequency generating device and the second high-frequency generating device when the medical ventilation device is in the high-frequency inspiratory phase, by generating high-frequency oscillations in the oxygen input branch and the air input branch.

31. The control method according to claim 20, wherein, The intake branch includes an oxygen input branch and an air input branch. A first one-way air intake device is provided on the oxygen input branch, and a second one-way air intake device is provided on the air input branch. The method further includes: The flow rate of oxygen input to the oxygen input branch is controlled by the first one-way air intake device, and the flow rate of air input to the air input branch is controlled by the second one-way air intake device. The step of generating high-frequency oscillations in the inspiratory branch of the breathing circuit using a high-frequency oscillation generator includes generating high-frequency oscillations in the oxygen input branch and the air input branch using the high-frequency oscillation generator.

32. The control method according to claim 31, wherein, The step of reducing the target amplitude of the medical ventilation device when the average pressure does not reach the target average pressure includes: If the pressure in the breathing circuit during the high-frequency exhalation phase causes the average pressure to fail to reach the target average pressure, the preset low pressure is increased. If the pressure in the breathing circuit during the high-frequency inhalation phase causes the average pressure to fall short of the target average pressure, the preset high pressure is reduced.

33. The control method according to claim 20, wherein, The method further includes: If the average pressure fails to reach the target average pressure within a preset time after the target amplitude of the control method is reduced, the prompting device in the medical ventilation equipment is controlled to output a prompting message.

34. The control method according to claim 20, wherein, The method further includes: if the average pressure reaches the target average pressure, controlling the breathing circuit with the target amplitude; or The method further includes: if the current output capacity of the medical ventilation device does not reach the maximum output capacity of the medical ventilation device, controlling the breathing circuit with the target amplitude.

35. The control method according to claim 20, wherein, The current operating current or voltage of the medical ventilation device indicates the current output capacity of the medical ventilation device.

36. The control method according to claim 20, wherein, The method further includes: Obtain the operating parameters of each device set in the gas source interface and the breathing circuit; The pressure in the breathing circuit is acquired during the formation of the high-frequency oscillation; The pressure amplitude corresponding to the breathing circuit is obtained based on the pressure in the breathing circuit. If the pressure amplitude corresponding to the breathing circuit does not reach the target amplitude, the operating parameters of each device are adjusted. The target amplitude is the difference between the preset high pressure corresponding to the breathing circuit during the high-frequency inhalation phase and the preset low pressure corresponding to the breathing circuit during the high-frequency exhalation phase.

37. The control method according to claim 36, wherein, If the pressure amplitude corresponding to the breathing circuit does not reach the target amplitude, adjusting the operating parameters of each device includes: If the pressure amplitude corresponding to the breathing circuit does not reach the target amplitude, compensation parameters for the operating parameters of each device are obtained based on the difference between the pressure amplitude corresponding to the breathing circuit and the target amplitude. The compensation parameters for the operating parameters of each device are used to adjust the operating parameters of each device.

38. The control method according to claim 37, wherein, The compensation parameters for obtaining the operating parameters of each device based on the difference between the pressure amplitude corresponding to the breathing circuit and the target amplitude include: If the pressure amplitude corresponding to the breathing circuit is less than the target amplitude, increase the pressure amplitude corresponding to the breathing circuit; If the pressure amplitude corresponding to the breathing circuit is greater than the target amplitude, the pressure amplitude corresponding to the breathing circuit is reduced.

39. A computer-readable storage medium storing executable instructions configured to cause a processor to execute the executable instructions to implement the control method of a medical ventilation device as claimed in any one of claims 20 to 38.

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