Medical device ventilation control method, system, storage medium and medical device

Abstract

The present invention is applicable to the technical field of medical devices, and provides a ventilation control method, system, storage medium and medical device for medical devices. The method includes calculating an initial ventilation pressure based on a target tidal volume and respiratory mechanics parameters measured by a tentative ventilation, and applying the initial ventilation pressure to pressure-controlled ventilation in the first respiratory cycle; monitoring the actual tidal volume of each respiratory cycle in real time, and determining whether the target tidal volume is reached within the target inhalation time; if not, adjusting the ventilation pressure of the next respiratory cycle according to the actual tidal volume and the target tidal volume; if so, determining whether the actual inhalation time is less than the target inhalation time; if it is less than the target inhalation time, immediately terminate the ventilation flow rate and enter the inhalation pause stage, and dynamically adjust the ventilation pressure of the next respiratory cycle according to the actual inhalation time and the target inhalation time of each respiratory cycle until the actual inhalation time is equal to the target inhalation time. The present invention solves the problem of tidal volume overshoot that may occur under the existing pressure adjustment mechanism.

Description

Technical Field

[0001] The present invention relates to the technical field of medical equipment, and in particular to a ventilation control method and system for medical equipment, a storage medium and medical equipment. Background Art

[0002] In clinical respiratory support, the Pressure Regulated Volume Control (PRVC) breathing mode is a widely used ventilation mode, which combines the advantages of pressure-controlled ventilation (PCV) and volume-controlled ventilation (VCV), and can ensure the stability of the delivered tidal volume in real-time adjustment. Its core goal is to dynamically adjust the inspiratory pressure (Pset) to match the tidal volume (VTreal) with the preset target (VTset) in each respiratory cycle, and after each respiratory cycle, the medical device (such as a ventilator or anesthesia machine) adjusts the inspiratory pressure of the next respiratory cycle in a fixed step according to the difference between the actual tidal volume and the target tidal volume.

[0003] However, when the target tidal volume is adjusted, or the patient's lung compliance and airway resistance change dramatically, the medical device's single-cycle pressure adjustment mechanism may not be able to adapt in time, resulting in an overshoot of tidal volume delivery (that is, the actual tidal volume exceeds the target tidal volume), especially during the pressure increase process, which can easily lead to overventilation of the patient and increase the risk of medical device-related complications. At the same time, refer to Figure 5 As shown in the figure, PRVC usually uses discrete step pressure adjustment, that is, the pressure is adjusted after each respiratory cycle. This lag may lead to overventilation. In addition, the traditional PRVC is based on the data of the previous cycle when adjusting the pressure, and cannot respond immediately to changes in the current respiratory cycle. For example, during a respiratory cycle, if the patient's lung mechanics suddenly changes, the medical device needs to adjust the pressure in the next cycle. The time difference in between causes a clinically significant deviation between the actual tidal volume and the target tidal volume.

[0004] For example, if the patient's lung compliance suddenly improves, and the medical device still uses the previous higher pressure, too much tidal volume will be delivered. Or in patients with acute respiratory distress syndrome (ARDS), their lung compliance may drop sharply in a short period of time. When the system increases the pressure sharply to maintain the tidal volume to compensate for the decrease in lung compliance, it may cause the pressure to be too high in the next ventilation cycle, causing the delivered tidal volume to be significantly higher than the safety threshold, increasing the risk of lung injury.

[0005] Therefore, the technical defect of this overshoot phenomenon not only affects the stability of ventilation parameters, but also may have a negative impact on the respiratory treatment of critically ill patients. How to achieve precise control of tidal volume output and avoid overventilation has become a technical problem that needs to be solved urgently in this field. Summary of the Invention

[0006] Based on this, the object of the present invention is to provide a ventilation control method, system, storage medium and medical device for medical devices, so as to fundamentally solve the problem of tidal volume overshoot that may occur under the existing pressure adjustment mechanism.

[0007] A ventilation control method for a medical device according to an embodiment of the present invention, the method includes:

[0008] Calculate an initial ventilation pressure according to the target tidal volume set by the user and the respiratory mechanics parameters measured by a tentative ventilation, and apply it to the pressure control ventilation of the first respiratory cycle;

[0009] Real-time monitor the actual tidal volume of each respiratory cycle, and judge whether the target tidal volume is reached within a preset target inhalation time;

[0010] If the target tidal volume is not reached within the target inhalation time, adjust the ventilation pressure of the next respiratory cycle according to the actual tidal volume and the target tidal volume;

[0011] If the target tidal volume is reached within the target inhalation time, judge whether the actual inhalation time is less than the target inhalation time;

[0012] If so, immediately terminate the ventilation flow rate and enter the inspiratory pause phase, and dynamically adjust the ventilation pressure of the next respiratory cycle according to the actual inhalation time and the target inhalation time of each respiratory cycle until the actual inhalation time is equal to the target inhalation time.

[0013] In addition, a ventilation control method for a medical device according to the above embodiment of the present invention may further have the following additional technical features:

[0014] Further, the step of calculating an initial ventilation pressure according to the target tidal volume set by the user and the respiratory mechanics parameters measured by a tentative ventilation, and applying it to the pressure control ventilation of the first respiratory cycle includes:

[0015] Deliver a test gas flow at a constant test pressure during the tentative ventilation stage, and monitor the actual tidal volume, plateau pressure, peak inspiratory pressure, positive end-expiratory pressure and peak inspiratory flow rate;

[0016] Calculate the lung compliance in the respiratory mechanics parameters according to the actual tidal volume, plateau pressure, and positive end-expiratory pressure of the ventilation;

[0017] Calculate the airway resistance in the respiratory mechanics parameters according to the peak inspiratory pressure, plateau pressure, and peak inspiratory flow rate of the ventilation;

[0018] Calculate the initial ventilation pressure according to the target tidal volume set by the user, lung compliance, airway resistance, peak inspiratory flow rate and positive end-expiratory pressure;

[0019] Load the initial ventilation pressure to the pressure control ventilation of the first respiratory cycle.

[0020] Further, the step of adjusting the ventilation pressure of the next respiratory cycle according to the actual tidal volume and the target tidal volume includes:

[0021] Calculate the tidal volume deviation value between the actual tidal volume and the target tidal volume;

[0022] Calculate and adjust the ventilation pressure of the next respiratory cycle according to the ventilation pressure, tidal volume deviation value and lung compliance adjustment coefficient of the current respiratory cycle.

[0023] Further, the step of dynamically adjusting the ventilation pressure of the next respiratory cycle according to the actual inspiratory time and the target inspiratory time of each respiratory cycle includes:

[0024] Calculate the time deviation ratio between the actual inspiratory time and the target inspiratory time;

[0025] When the time deviation ratio is greater than the first deviation ratio, determine and adjust the ventilation pressure of the next respiratory cycle according to the preset adjustment coefficient of the ventilation pressure of the current respiratory cycle;

[0026] When the time deviation ratio is less than the second deviation ratio, determine and adjust the ventilation pressure of the next respiratory cycle according to the ventilation pressure of the current respiratory cycle and the preset pressure step;

[0027] When the time deviation ratio is less than the first deviation ratio and greater than the second deviation ratio, determine and adjust the ventilation pressure of the next respiratory cycle according to the ventilation pressure of the current respiratory cycle and the time deviation ratio.

[0028] Further, the method further includes:

[0029] When a new target tidal volume is obtained by the user, recalculate the initial ventilation pressure according to the new target tidal volume and the respiratory mechanics parameters, and apply it to the pressure control ventilation of the next respiratory cycle; or

[0030] When it is detected that the change rate of the current respiratory mechanics parameters exceeds the predetermined change rate range, recalculate the initial ventilation pressure according to the target tidal volume and the current respiratory mechanics parameters, and apply it to the pressure control ventilation of the next respiratory cycle.

[0031] Further, the method further includes:

[0032] In all respiratory cycles after the first respiratory cycle, calculate the cumulative deviation amount of the actual tidal volume and the target tidal volume in real time, and determine whether the cumulative deviation amount exceeds the preset deviation amount threshold;

[0033] If so, forcefully terminate the current respiratory cycle, trigger an alarm, reset the ventilation pressure to the initial ventilation pressure, and restart the tentative ventilation.

[0034] Furthermore, the method further includes:

[0035] Calculate the change rate of the pressure adjustment amount between the ventilation pressure adjusted to the next respiratory cycle and the ventilation pressure of the current respiratory cycle, and determine whether the change rate of the pressure adjustment amount exceeds a preset maximum change rate;

[0036] If so, determine the ventilation pressure of the next respiratory cycle based on the ventilation pressure of the current respiratory cycle and the preset maximum change rate, and make an adjustment.

[0037] Another object of an embodiment of the present invention is to provide a ventilation control system for a medical device, the system includes:

[0038] Another object of an embodiment of the present invention is to provide a storage medium, which stores a program, and when the program is executed by a processor, it implements the medical device ventilation control method as described above.

[0039] Another object of an embodiment of the present invention is to provide a medical device, including a memory, a processor, and a program stored on the memory and executable on the processor. When the processor executes the program, it implements the medical device ventilation control method as described above.

[0040] The medical device ventilation control method provided by the embodiment of the present invention calculates the initial ventilation pressure based on the target tidal volume set by the user and the respiratory mechanics parameters measured by the tentative ventilation, and applies it to the first respiratory cycle, so that it is possible to set a suitable initial pressure according to the actual respiratory mechanics of the individual, avoiding the problems of excessive or insufficient initial pressure that may occur in the traditional ventilation pressure setting, and then achieving more accurate tidal volume control; by real-time monitoring the actual tidal volume of each respiratory cycle, and judging whether the target tidal volume is reached within the preset target inhalation time, and the actual inhalation time is less than the target inhalation time, immediately terminate the ventilation flow rate and enter the inhalation pause stage, so that the actual tidal volume is maintained at the target tidal volume without ventilation, avoiding the problem of tidal volume overshoot caused by too high ventilation pressure, and adjusting the ventilation pressure of the next respiratory cycle according to the difference between the actual tidal volume and the target tidal volume. This dynamic adjustment mechanism enables the medical device to continuously optimize the ventilation pressure according to the feedback of each respiratory cycle, avoiding tidal volume deviation caused by the adjustment of the target tidal volume or drastic changes in the respiratory mechanics parameters of the patient, and solving the problem of tidal volume overshoot that may occur under the existing pressure adjustment mechanism. Description of the Drawings

[0041] Figure 1Flow chart of the ventilation control method for a medical device in the first embodiment of the present invention;

[0042] Figure 2 Structural diagram of the ventilation control system for a medical device in the second embodiment of the present invention;

[0043] Figure 3 Structural diagram of a medical device in the third embodiment of the present invention;

[0044] Figure 4 Pressure and flow curve diagram of target tidal volume adjustment in the ventilation control method for a medical device in the first embodiment of the present invention;

[0045] Figure 5 Pressure and flow curve diagram of target tidal volume adjustment in a medical device of the prior art;

[0046] The following specific embodiments will further illustrate the present invention in conjunction with the above-mentioned drawings. Specific Embodiments

[0047] For ease of understanding of the present invention, the present invention will be described more comprehensively below with reference to the relevant drawings. Several embodiments of the present invention are shown in the drawings. However, the present invention can be implemented in many different forms and is not limited to the embodiments described herein. On the contrary, these embodiments are provided to make the disclosure of the present invention more thorough and comprehensive.

[0048] It should be noted that when an element is referred to as being "fixed to" another element, it can be directly on the other element or there can also be an intermediate element. When an element is considered to be "connected" to another element, it can be directly connected to the other element or there may be an intermediate element at the same time. The terms "vertical", "horizontal", "left", "right" and similar expressions used herein are for illustrative purposes only.

[0049] Unless otherwise defined, all technical and scientific terms used herein have the same meaning as commonly understood by those of ordinary skill in the technical field to which the present invention belongs. The terms used herein in the specification of the present invention are only for the purpose of describing specific embodiments and are not intended to limit the present invention. The term "and / or" used herein includes any and all combinations of one or more of the related listed items.

[0050] Embodiment 1

[0051] Please refer to Figure 1 , which shows the ventilation control method for a medical device in the first embodiment of the present invention. For ease of explanation, only the parts related to the embodiments of the present invention are shown. The ventilation control method for a medical device provided by the embodiments of the present invention includes:

[0052] Step S10: Calculate an initial ventilation pressure based on a target tidal volume set by a user and respiratory mechanics parameters measured by a tentative ventilation, and apply the initial ventilation pressure to pressure-controlled ventilation in a first respiratory cycle.

[0053] Among them, in an embodiment of the present invention, the method is applied to a medical device such as a ventilator or an anesthesia machine, and is an improved ventilation control method for the PRVC ventilation mode in existing medical devices. The control logic of the PRVC (Pressure Regulated Volume Control) ventilation mode is to dynamically adjust the inspiratory pressure to ensure that the actual tidal volume stably approaches a preset target tidal volume in the pressure-controlled ventilation mode. The tidal volume refers to the volume of gas entering or leaving the lungs during each breath. Specifically, taking a ventilator as an example of the medical device, its specific working principle is that medical staff preset basic parameters such as the target tidal volume, respiratory rate, inspiratory time, and positive end-expiratory pressure in advance. Further, the ventilator first delivers gas at a relatively low pressure, and real-time monitors the patient's lung compliance and airway resistance through flow and pressure sensors, and calculates the ventilation pressure required to reach the target tidal volume. After each breath, the ventilator automatically adjusts the next inspiratory pressure according to the feedback of the previous breath (such as the actual tidal volume) (specifically adjusted step by step in a stepwise manner). If the actual tidal volume is lower than the target tidal volume, the pressure is appropriately increased; if it is higher than the target value, the pressure is decreased. During the inspiratory phase (i.e., the inspiratory phase), the ventilator ventilates in a pressure control mode, but ensures that the finally output actual tidal volume approaches the target tidal volume by dynamically adjusting the pressure upper limit. However, when the target tidal volume is adjusted, or when the patient's lung compliance and airway resistance change, the single-cycle pressure adjustment mechanism of the ventilator may not be able to adapt in time, resulting in an overshoot phenomenon in tidal volume delivery. Therefore, the embodiment of the present invention is improved based on the above PRVC ventilation mode to solve the overshoot phenomenon in tidal volume delivery.

[0054] Specifically, the step of calculating an initial ventilation pressure based on a target tidal volume set by a user and respiratory mechanics parameters measured by a tentative ventilation, and applying the initial ventilation pressure to pressure-controlled ventilation in a first respiratory cycle specifically includes:

[0055] Deliver a test gas flow at a constant test pressure during the tentative ventilation stage, and monitor the actual tidal volume, plateau pressure, peak inspiratory pressure, positive end-expiratory pressure, and peak inspiratory flow rate.

[0056] Calculate the lung compliance in the respiratory mechanics parameters based on the actual tidal volume, plateau pressure, and positive end-expiratory pressure of the ventilation.

[0057] Calculate the airway resistance in the respiratory mechanics parameters based on the peak inspiratory pressure, plateau pressure, and peak inspiratory flow rate of the ventilation.

[0058] Calculate the initial ventilation pressure based on the target tidal volume, lung compliance, airway resistance, peak inspiratory flow rate, and positive end-expiratory pressure set by the user;

[0059] Load the initial ventilation pressure into the pressure control ventilation of the first respiratory cycle.

[0060] Among them, when the medical device determines the respiratory mechanics parameters for the first time at startup, it will enter the exploratory ventilation stage, which specifically includes delivering air flow to the patient's airway at a preset constant test pressure, where this pressure remains unchanged and is used to measure the patient's lung response. During the exploratory ventilation process, it is necessary to monitor the actual tidal volume, plateau pressure, positive end-expiratory pressure, and peak inspiratory flow rate in real time. Among them, the actual tidal volume refers to the volume of gas inhaled at this constant pressure; the plateau pressure refers to the pressure value when the airway pressure reaches a stable state (no air flow, usually the pressure during the apnea period); the peak inspiratory pressure refers to the pressure value when the airway pressure reaches the peak; the positive end-expiratory pressure refers to the pressure remaining in the airway at the end of exhalation (to prevent lung collapse), which is usually set by the user; the peak inspiratory flow rate refers to the highest air flow rate during inhalation. Then, based on the data obtained from the exploratory ventilation, two key respiratory mechanics parameters of the patient are calculated, namely lung compliance and airway resistance. Among them, lung compliance (C) represents the patient's lung's ability to expand in response to air flow, that is, the volume change caused by a unit pressure change, which is specifically calculated based on the actual tidal volume, plateau pressure, and positive end-expiratory pressure. Among them, airway resistance (R) represents the resistance of the patient's gas flow in the airway, which is specifically calculated based on the peak inspiratory pressure, plateau pressure, and peak inspiratory flow rate of ventilation. Then, based on the obtained peak inspiratory flow rate and positive end-expiratory pressure, the calculated lung compliance and airway resistance, and the target tidal volume set by the user, the initial ventilation pressure is determined. Specifically, the initial ventilation pressure needs to overcome both the elastic resistance (related to compliance) and the airway resistance (related to flow rate) at the same time. Among them, the elastic resistance is determined by the target tidal volume and lung compliance and reflects the pressure required for alveolar expansion. The airway resistance is determined by the peak inspiratory flow rate and airway resistance and reflects the viscous resistance of gas flow. At the same time, the positive end-expiratory pressure is the base pressure, set by the user. At this time, the initial ventilation pressure is determined based on the base pressure composed of the above positive end-expiratory pressure, the elastic resistance calculated from the target tidal volume and lung compliance, and the airway resistance calculated from the peak inspiratory flow rate and airway resistance. Once the initial ventilation pressure is calculated, it is loaded as the pressure control value of the first respiratory cycle into the pressure control ventilation of the first respiratory cycle, and the medical device controls the delivery of gas according to the calculated initial ventilation pressure to ensure that the volume of gas inhaled by the patient reaches the target tidal volume.

[0061] Furthermore, when using the pressure control ventilation (PCV) mode, at least two independent tentative ventilations are performed. The constant test pressure for each test is set to different step values, and the duration of a single test is not less than five complete respiratory cycles. It should be noted that the selection of the pressure level should be determined according to the patient's condition and clinical experience to avoid damage caused by excessive pressure. At the same time, the corresponding actual tidal volume, plateau pressure, positive end-expiratory pressure data, and peak inspiratory flow rate are recorded after each test, and the lung compliance and airway resistance are calculated accordingly. If the error of the lung compliance or airway resistance calculated twice exceeds the preset error value (specifically, for example, 10%), then an additional next test is triggered. At this time, different test pressures are used, and the median or weighted average of the multiple test results is taken as the final lung compliance parameter and airway resistance parameter. If the range (the difference between the maximum value and the minimum value) of the three test results still exceeds the preset range value (specifically, for example, 15%), it is determined that the airway response is abnormal (there may be non-linear characteristics or measurement errors). At this time, the ventilation mode is switched to the volume control ventilation (VCV) mode and an alarm is triggered.

[0062] It should be noted that in an embodiment of the present invention, during the tentative ventilation process, if the patient has strong spontaneous breathing, it may cause antagonism with the medical device ventilation, resulting in discomfort and measurement errors. Therefore, when the patient's spontaneous breathing effort is detected, it is automatically switched to the synchronized ventilation mode. Specifically, during the inspiratory phase of the tentative ventilation, the airflow velocity and airway pressure are monitored. A negative flow velocity threshold and a pressure drop threshold are preset in the medical device. When the detected negative airflow velocity is lower than the negative flow velocity threshold (indicating that the patient inhales actively) or the detected airway pressure drop exceeds the pressure drop threshold, it is determined that there is a spontaneous breathing effort. At this time, it is switched to the pressure support ventilation (PSV) mode. In the PSV mode, the medical device provides a preset pressure support level to help the patient inhale. When the patient's spontaneous breathing weakens or disappears, it is automatically switched back to the original tentative ventilation mode accordingly.

[0063] Step S20, continuously monitor the actual tidal volume of each respiratory cycle, and determine whether the target tidal volume is reached within the preset target inspiratory time;

[0064] Among them, in an embodiment of the present invention, after determining the initial ventilation pressure and controlling the gas for the first ventilation delivery, the flow rate is calculated in real time by a flow sensor placed at the exhalation port of the medical device or between the inhalation / exhalation pipelines, and the analog signal output by the flow sensor is converted into a digital signal. After filtering the digital signal to remove noise and interference, the flow signal is integrated to obtain the real-time tidal volume. At this time, the actual tidal volume is monitored in real time and it is judged whether the target tidal volume is reached within the preset target inhalation time. When it is judged that the target tidal volume is not reached within the preset target inhalation time, step S30 is executed; when it is judged that the target tidal volume is reached within the preset target inhalation time, step S40 is executed. It should be noted that due to reasons such as sensor drift, there may be errors in the integration result. Therefore, drift compensation is required. For example, at the beginning of each breathing cycle, the integration value is reset to zero.

[0065] Step S30: Adjust the ventilation pressure of the next breathing cycle according to the actual tidal volume and the target tidal volume;

[0066] Among them, when the target tidal volume is not reached within the preset target inhalation time, it means that the amount of gas inhaled by the patient is insufficient. At this time, the ventilation pressure needs to be increased accordingly to gradually increase the actual tidal volume to reach the target tidal volume. Specifically, the above step of adjusting the ventilation pressure of the next breathing cycle according to the actual tidal volume and the target tidal volume includes:

[0067] Calculate the tidal volume deviation value between the actual tidal volume and the target tidal volume;

[0068] Calculate and adjust the ventilation pressure of the next breathing cycle according to the ventilation pressure, tidal volume deviation value and lung compliance adjustment coefficient of the current breathing cycle.

[0069] Specifically, when the actual tidal volume is less than the target tidal volume, it indicates that the current pressure is insufficient to deliver enough tidal volume, and at this time, the ventilation pressure needs to be increased. Since the tidal volume is mainly determined by lung compliance under pressure control, lung compliance should be considered when adjusting the pressure. Among them, if the lung compliance is high (that is, the "elasticity" of the lung is good), it means that a smaller pressure change can make the lungs inhale or exhale more gas. If the lung compliance is low (such as lung stiffness), it means that a larger pressure change is required to make the lungs inhale or exhale the same amount of gas. At this time, the increase in tidal volume brought by the same pressure increment is small, so a greater pressure compensation is required. At this time, the lung compliance adjustment coefficient is inversely proportional to the lung compliance. Therefore, when the lung compliance is low here, the ventilation pressure adjustment amount increases, so as to more effectively compensate for the insufficient tidal volume caused by low compliance. At this time, its ventilation pressure adjustment amount is jointly determined by the lung compliance adjustment coefficient and the tidal volume deviation value. Therefore, the ventilation pressure of the next breathing cycle is determined according to the ventilation pressure of the current breathing cycle and the ventilation pressure adjustment amount jointly determined by the lung compliance adjustment coefficient and the tidal volume deviation value, and the ventilation pressure of the next breathing cycle is adjusted after determination.

[0070] Step S40, determine whether the actual inspiratory time is less than the target inspiratory time;

[0071] Among them, in an embodiment of the present invention, when it is determined that the actual inspiratory time is less than the target inspiratory time, that is, the ventilation of the target tidal volume is completed in advance. If continuous ventilation is carried out until the target inspiratory time, the situation where the actual tidal volume is greater than the target tidal volume will occur. Therefore, to avoid the generation of tidal volume overshoot, it directly executes step S50; when it is determined that the actual inspiratory time is equal to the target inspiratory time, it means that it can control the actual tidal volume ventilated in the inspiratory phase to reach the target tidal volume, and no operation is performed at this time.

[0072] Step S50, immediately terminate the ventilation flow rate and enter the inspiratory pause phase, and dynamically adjust the ventilation pressure of the next breathing cycle according to the actual inspiratory time and the target inspiratory time of each breathing cycle until the actual inspiratory time is equal to the target inspiratory time;

[0073] Among them, in an embodiment of the present invention, when it is determined that the actual inspiratory time is less than the target inspiratory time, at this time, the ventilation flow rate is immediately terminated and the inspiratory pause phase is entered. At this time, when the supply flow rate drops to zero, the medical device closes the inspiratory valve and keeps the expiratory valve closed to completely block the possible residual airflow and eliminate the overshoot caused by continuous gas supply in traditional pressure control. Specifically, refer to Figure 4As shown, the complete respiratory cycle of the medical device includes an inhalation phase (inhalation stage) and an exhalation phase (exhalation stage). During the inhalation phase, the medical device delivers gas to the patient, and during the exhalation phase, the patient exhales gas into the circuit. At this time, during the inhalation stage, a pressure-controlled ventilation mode is used for pressure control. When the inhalation time ends, the medical device switches to the exhalation stage, and at this time, the ventilation pressure drops to the plateau pressure. When adjusting the tidal volume, after the end of the current respiratory cycle, a stepwise adjustment of the ventilation pressure is performed based on the feedback of the actual tidal volume and the target tidal volume. Therefore, at the beginning of a new respiratory cycle, the medical device applies the adjusted ventilation pressure and keeps it fixed within the new cycle until the next respiratory cycle is adjusted. Through this design, the pressure is kept stable within each cycle, making it easier to estimate the tidal volume. Further refer to Figure 4 As shown, in pressure-controlled ventilation, the flow rate during the inhalation stage is driven by the pressure of the gas provided by the medical device into the lungs, and at this time, the flow rate is in the positive direction (into the lungs). And under a constant ventilation pressure, as the alveoli gradually fill, the alveolar pressure increases, and the driving pressure difference gradually decreases, resulting in a natural attenuation of the flow rate. At this time, the flow rate is always in the positive direction and the value decreases. When the target inhalation time is reached, the medical device stops delivering gas, the exhalation valve opens, and it switches to the exhalation stage. During the exhalation stage, the medical device stops applying pressure, and the patient exhales gas passively relying on the elastic recoil force of the lungs. At this time, the direction of the flow rate is reversed (negative direction), that is, the gas flows out of the lungs.

[0074] Among them, when immediately terminating the ventilation flow rate and entering the inspiratory pause stage, the ventilation pressure in the airway is adjusted accordingly. Specifically, it can be directly adjusted to the ventilation pressure of the next respiratory cycle, or the ventilation pressure can be gradually adjusted and reduced. Refer to Figure 4 As shown, when the target tidal volume is reached within the target inhalation time and the actual inhalation time is less than the target inhalation time, the ventilation flow rate is immediately terminated and enters the inspiratory pause stage. At this time, the ventilation flow rate directly drops to 0, and the ventilation pressure is also adjusted accordingly to the ventilation pressure of the next respiratory cycle. When the inspiratory phase of the current respiratory cycle is completed and enters the respiratory phase, the inspiratory valve is opened and the airway pressure is maintained at the plateau pressure level.

[0075] Among them, the steps of dynamically adjusting the ventilation pressure of the next respiratory cycle according to the actual inhalation time and the target inhalation time of each respiratory cycle include:

[0076] Calculate the time deviation ratio between the actual inhalation time and the target inhalation time;

[0077] When the time deviation ratio is greater than the first deviation ratio, the ventilation pressure of the next respiratory cycle is determined according to the preset adjustment coefficient of the ventilation pressure of the current respiratory cycle and adjusted;

[0078] When the time deviation ratio is less than the second deviation ratio, the ventilation pressure for the next breathing cycle is determined based on the ventilation pressure of the current breathing cycle and a preset pressure step size and adjusted.

[0079] When the time deviation ratio is less than the first deviation ratio and greater than the second deviation ratio, the ventilation pressure for the next breathing cycle is determined based on the ventilation pressure of the current breathing cycle and the time deviation ratio and adjusted.

[0080] Specifically, when it is determined that the actual inhalation time is less than the target inhalation time, that is, the ventilation of the target tidal volume is completed in advance. If ventilation continues until the target inhalation time, the actual tidal volume will be greater than the target tidal volume, and the pressure will be too high at this time, so the pressure needs to be reduced. Specifically, first calculate the time deviation ratio between the actual inhalation time and the target inhalation time, and then the time deviation ratio will take advantage of staged adjustment. For example, when the actual inhalation time is significantly less than the target inhalation time, it means that the current ventilation pressure may be too high and sufficient tidal volume is delivered within the predetermined time in advance, so the pressure needs to be greatly reduced. At this time, stepwise adjustment is used to quickly correct the deviation; in the case of medium deviation, such as when the time deviation ratio is less than the first deviation ratio and greater than the second deviation ratio, linear adjustment (such as adjusting according to the time deviation ratio) can balance the response speed and stability and avoid overshoot. When the deviation is very small, such as when the time deviation ratio is less than the second deviation ratio, the fine-tuning mode gradually reduces the pressure according to the preset pressure step size at this time to ensure the accuracy of the adjustment and prevent discomfort caused by pressure fluctuations to the patient. Therefore, by rapidly approaching the target with a high-pressure step in the case of large deviation; and making small-step corrections to prevent oscillation in the case of small deviation, dynamic adaptability, rapid response, and stable pressure are achieved.

[0081] Among them, the above preset adjustment coefficient is mainly determined according to airway resistance. Specifically, the fact that the actual tidal volume reaches the target tidal volume too quickly may be related not only to the ventilation pressure but also to the airway resistance. For example, if the airway resistance suddenly decreases (such as the clearance of secretions), the flow rate increases at the same pressure, resulting in an increase in tidal volume. Therefore, the preset adjustment coefficient needs to consider the airway resistance factor, and the airway resistance is the dominant factor, that is, the preset adjustment coefficient is determined according to the airway resistance, and the preset adjustment coefficient is proportional to the airway resistance. Specifically, when the airway resistance is higher, the preset adjustment coefficient is larger, and the reduction amplitude of the ventilation pressure is greater, that is, more significant adjustments are required at high airway resistance to avoid excessive tidal volume. It should be noted that in other embodiments of the present invention, the preset adjustment coefficient is also related to the change rate of lung compliance and is proportional: when the change rate of lung compliance exceeds a preset threshold, the preset adjustment coefficient needs to be increased accordingly to accelerate the correction of the ventilation pressure. That is to say, the step of determining the ventilation pressure of the next respiratory cycle according to the preset adjustment coefficient of the ventilation pressure of the current respiratory cycle and making adjustments includes judging whether the change rate of the lung compliance within the preset number of measured respiratory cycles exceeds the preset threshold; if so, determining the preset adjustment coefficient according to the currently measured airway resistance and the change rate of lung compliance.

[0082] Among them, in one embodiment of the present invention, the method further includes:

[0083] When a user re - sets a new target tidal volume, recalculate the initial ventilation pressure according to the new target tidal volume and respiratory mechanics parameters, and apply it to the pressure - controlled ventilation of the next respiratory cycle; or

[0084] When it is detected that the change rate of the current respiratory mechanics parameters exceeds a predetermined change rate range, recalculate the initial ventilation pressure according to the target tidal volume and the current respiratory mechanics parameters, and apply it to the pressure - controlled ventilation of the next respiratory cycle.

[0085] Specifically, when the medical device detects that the user inputs a new target tidal volume, it will re - conduct tentative ventilation monitoring to obtain the patient's respiratory mechanics parameters. Then, using the new target tidal volume and the current respiratory mechanics parameters, etc., according to the same calculation method as when starting for the first time, it recalculates a new initial ventilation pressure and sets the calculated new initial ventilation pressure as the target pressure for pressure - controlled ventilation in the next respiratory cycle. At the beginning of the next respiratory cycle, gas will be delivered to the patient according to the new initial ventilation pressure value. Meanwhile, the medical device continuously monitors the patient's respiratory mechanics parameters (or periodically repeats tentative ventilation), such as using the data of each respiratory cycle to estimate the respiratory mechanics parameters in real - time (for example, by analyzing the pressure - volume curve or flow - volume curve) or automatically repeating a short - term tentative ventilation every certain period (such as 15 minutes, 30 minutes, or 1 hour) to obtain more accurate respiratory mechanics parameters. At this time, the medical device calculates the change rate of the current respiratory mechanics parameters (C and R) relative to the previous measured values (such as the result of the previous tentative ventilation), and compares the calculated change rate with the threshold of the preset change rate of respiratory mechanics parameters. If the change rate of any one of the respiratory mechanics parameters (C or R) exceeds the corresponding predetermined change rate range, it is determined that a significant change has occurred in the patient's respiratory condition, and at this time, it is necessary to recalculate the initial ventilation pressure. At this time, the medical device uses the current target tidal volume and the latest measured current respiratory mechanics to recalculate a new initial ventilation pressure according to the same calculation method as when starting for the first time, and sets it as the target ventilation pressure for pressure - controlled ventilation in the next respiratory cycle. By dynamically adjusting the ventilation parameters according to the patient's individual differences and disease changes, it can promptly respond to the changes in respiratory mechanics parameters and avoid ventilation insufficiency or over - ventilation caused by improper parameter settings, ensuring that the ventilation treatment is always in the best state and improving the treatment effect.

[0086] Among them, during the continuous gas delivery process, the medical device not only pays attention to the deviation between the actual tidal volume and the target tidal volume in each respiratory cycle, but also accumulatively calculates these deviations. If the accumulated deviation amount is too large, it indicates that there is a persistent problem in ventilation control, and there may be situations such as air leakage, airway obstruction, or sudden change in the patient's condition. At this time, immediate measures need to be taken to ensure the patient's safety. Therefore, in an embodiment of the present invention, the method further includes:

[0087] In all respiratory cycles after the first respiratory cycle, the cumulative deviation amount between the actual tidal volume and the target tidal volume is calculated in real - time, and it is judged whether the cumulative deviation amount exceeds the preset deviation amount threshold;

[0088] If so, the current respiratory cycle is forcibly terminated and an alarm is triggered. At the same time, the ventilation pressure is reset to the initial ventilation pressure and the tentative ventilation is restarted.

[0089] Specifically, after each respiratory cycle ends, the medical device calculates the deviation value between the actual tidal volume and the target tidal volume, and accumulates the deviation value into a "cumulative deviation amount" variable. At this time, the cumulative deviation amount reflects the difference between the total gas volume actually delivered to the patient and the total gas volume expected to be delivered from the start of ventilation to the present. A preset deviation amount threshold is preset inside the medical device. This threshold can be an absolute value (such as 500 mL) or a percentage of the target tidal volume (such as 20%). After each respiratory cycle ends, the medical device compares the absolute value of the cumulative deviation amount with the preset deviation amount threshold. If the absolute value of the cumulative deviation amount exceeds the preset deviation amount threshold, it indicates that the accumulated deviation is too large. The medical device determines that there is a serious problem and needs to take immediate protective measures. At this time, the medical device forcibly terminates the current respiratory cycle, that is, immediately stops delivering gas, to prevent excessive or insufficient gas from being delivered to the patient. At the same time, it triggers an alarm to emit an audible and visual alarm to alert medical staff. In addition, the ventilation pressure is reset and a tentative ventilation is restarted. Specifically, the ventilation pressure is reset to the initial ventilation pressure (the pressure calculated based on the initial tentative ventilation). A tentative ventilation is automatically restarted to re-evaluate the patient's respiratory mechanics parameters. In some cases, it can also be directly switched to the volume control mode. It should be noted that after the protection mechanism is triggered, or after each tentative ventilation is started, the medical device resets the "cumulative deviation amount" variable to zero and starts accumulating and calculating again. Therefore, by detecting and handling persistent ventilation deviations in a timely manner, it prevents serious consequences caused by cumulative errors. At the same time, it avoids long-term ineffective ventilation caused by reasons such as air leakage, airway obstruction, and sudden changes in the patient's condition. The automatic triggering of the protection mechanism and the reset operation can reduce the burden on medical staff.

[0090] Among them, when the medical device adjusts the ventilation pressure, in order to avoid discomfort or lung injury to the patient caused by too rapid pressure change, it is necessary to limit the speed of pressure adjustment to ensure a smooth transition of the pressure. Therefore, in an embodiment of the present invention, the method further includes:

[0091] Calculating the change rate of the pressure adjustment amount between the ventilation pressure adjusted to the next respiratory cycle and the ventilation pressure of the current respiratory cycle, and determining whether the change rate of the pressure adjustment amount exceeds a preset maximum change rate;

[0092] If so, determining the ventilation pressure of the next respiratory cycle based on the ventilation pressure of the current respiratory cycle and the preset maximum change rate and making an adjustment.

[0093] Specifically, after each respiratory cycle ends, the medical device calculates a preliminary pressure adjustment amount (i.e., how much pressure should be adjusted if speed limit is not considered) based on factors such as the deviation between the actual tidal volume and the target tidal volume, and the lung compliance adjustment coefficient. At the same time, the medical device also records the previous actual pressure adjustment amount (i.e., how much pressure was actually adjusted in the previous respiratory cycle). At this time, the preliminary pressure adjustment amount of this time is compared with the previous actual pressure adjustment amount, and the difference between the two is calculated, that is, the change amount of the pressure adjustment amount. At this time, the change amount of the pressure adjustment amount is divided by the time of the respiratory cycle (or a fixed time interval) to obtain the change rate of the pressure adjustment amount. Among them, a maximum pressure adjustment rate limit value is preset inside the medical device (for example, the pressure change does not exceed 2 cmH2O per second). At this time, the medical device compares the calculated change rate of the pressure adjustment amount with the preset maximum change rate. If the change rate of the pressure adjustment amount does not exceed the preset maximum change rate, the actual pressure adjustment amount of this time is equal to the preliminary pressure adjustment amount, and the adjustment is made according to the calculation result at this time. If the change rate of the pressure adjustment amount exceeds the preset maximum change rate, the preliminary pressure adjustment amount needs to be limited so that its change rate does not exceed the preset maximum change rate. Specifically, calculate the maximum allowable change amount allowed for this time under the preset maximum change rate limit. If the absolute value of the preliminary pressure adjustment amount is greater than the maximum allowable change amount, set the actual pressure adjustment amount to the maximum allowable change amount (and maintain the same positive or negative sign as the preliminary pressure adjustment amount). If the absolute value of the preliminary pressure adjustment amount is less than the maximum allowable change amount, set the actual pressure adjustment amount to the preliminary pressure adjustment amount. Then, add (or subtract) the finally determined actual pressure adjustment amount to the ventilation pressure of the current respiratory cycle to obtain the ventilation pressure to be used in the next respiratory cycle. Then, at the beginning of the next respiratory cycle, the medical device delivers gas to the patient according to the new ventilation pressure value. At the same time, record the actual pressure adjustment amount of this time for calculating the change rate of the pressure adjustment amount next time. At this time, through the pressure adjustment rate limit, it is possible to avoid discomfort or lung injury caused by rapid pressure changes, make the pressure transition smoother, improve the patient's tolerance, provide more comfortable and effective ventilation support for the patient, and help reduce the fluctuation of ventilation parameters and improve the control accuracy.

[0094] In summary, in the medical device ventilation control method in the above embodiments of the present invention, by calculating the initial ventilation pressure based on the target tidal volume set by the user and the respiratory mechanics parameters measured by the exploratory ventilation and applying it to the first respiratory cycle, it is possible to set an appropriate initial pressure according to the actual respiratory mechanics of the individual, avoiding the problems of excessive or insufficient initial pressure that may occur in the traditional ventilation pressure setting, and thus achieving more accurate tidal volume control; by real-time monitoring the actual tidal volume of each respiratory cycle and determining whether the target tidal volume is reached within the preset target inhalation time, and if the actual inhalation time is less than the target inhalation time, the ventilation flow rate is immediately terminated and the inhalation pause phase is entered, so that the actual tidal volume is maintained at the target tidal volume without ventilation, avoiding the problem of tidal volume overshoot caused by excessive ventilation pressure, and adjusting the ventilation pressure of the next respiratory cycle according to the difference between the actual tidal volume and the target tidal volume. This dynamic adjustment mechanism enables the medical device to continuously optimize the ventilation pressure according to the feedback of each respiratory cycle, avoiding tidal volume deviation caused by the adjustment of the target tidal volume or drastic changes in the patient's respiratory mechanics parameters, and solving the problem of tidal volume overshoot that may occur under the existing pressure adjustment mechanism.

[0095] Embodiment 2

[0096] Please refer to Figure 2 , which is a schematic structural diagram of a medical device ventilation control system provided by the second embodiment of the present invention. For the convenience of description, only the parts related to the embodiments of the present invention are shown. The system includes:

[0097] An initial ventilation pressure calculation module 110, configured to calculate an initial ventilation pressure based on the target tidal volume set by the user and the respiratory mechanics parameters measured by the exploratory ventilation and apply it to the pressure control ventilation of the first respiratory cycle;

[0098] A tidal volume monitoring and judging module 120, configured to real-time monitor the actual tidal volume of each respiratory cycle and judge whether the target tidal volume is reached within the preset target inhalation time;

[0099] A first ventilation pressure adjustment module 130, configured to adjust the ventilation pressure of the next respiratory cycle according to the actual tidal volume and the target tidal volume if the target tidal volume is not reached within the target inhalation time;

[0100] An inhalation time judging module 140, configured to judge whether the actual inhalation time is less than the target inhalation time if the target tidal volume is reached within the target inhalation time;

[0101] The second ventilation pressure adjustment module 150 is configured to immediately terminate the ventilation flow rate and enter the inspiratory pause phase when the inspiratory time determination module determines that the actual inspiratory time is less than the target inspiratory time, and dynamically adjust the ventilation pressure of the next respiratory cycle according to the actual inspiratory time and the target inspiratory time of each respiratory cycle until the actual inspiratory time is equal to the target inspiratory time.

[0102] Further, in an embodiment of the present invention, the initial ventilation pressure calculation module 110 includes:

[0103] A data monitoring unit, configured to deliver a test gas flow at a constant test pressure during the tentative ventilation phase, and monitor the actual tidal volume, plateau pressure, peak inspiratory pressure, positive end-expiratory pressure, and peak inspiratory flow rate;

[0104] A lung compliance calculation unit, configured to calculate the lung compliance in the respiratory mechanics parameters according to the actual tidal volume, plateau pressure, and positive end-expiratory pressure of the ventilation;

[0105] An airway resistance calculation unit, configured to calculate the airway resistance in the respiratory mechanics parameters according to the peak inspiratory pressure, plateau pressure, and peak inspiratory flow rate of the ventilation;

[0106] An initial ventilation pressure calculation unit, configured to calculate the initial ventilation pressure according to the target tidal volume, lung compliance, airway resistance, peak inspiratory flow rate, and positive end-expiratory pressure set by the user;

[0107] A ventilation control unit, configured to load the initial ventilation pressure to the pressure control ventilation of the first respiratory cycle.

[0108] Further, in an embodiment of the present invention, the first ventilation pressure adjustment module 130 includes:

[0109] A tidal volume deviation value calculation unit, configured to calculate the tidal volume deviation value between the actual tidal volume and the target tidal volume;

[0110] A first ventilation pressure adjustment unit, configured to adjust the ventilation pressure of the next respiratory cycle according to the ventilation pressure, tidal volume deviation value, and lung compliance adjustment coefficient of the current respiratory cycle.

[0111] Further, in an embodiment of the present invention, the second ventilation pressure adjustment module 150 includes:

[0112] A time deviation ratio calculation unit, configured to calculate the time deviation ratio between the actual inspiratory time and the target inspiratory time;

[0113] A second ventilation pressure adjustment unit, configured to, when the time deviation ratio is greater than the first deviation ratio, determine the ventilation pressure of the next respiratory cycle according to the preset adjustment coefficient of the ventilation pressure of the current respiratory cycle and perform adjustment;

[0114] A third ventilation pressure adjustment unit, configured to, when the time deviation ratio is less than the second deviation ratio, determine and adjust the ventilation pressure for the next respiratory cycle according to the ventilation pressure of the current respiratory cycle and a preset pressure step size;

[0115] A fourth ventilation pressure adjustment unit, configured to, when the time deviation ratio is less than the first deviation ratio and greater than the second deviation ratio, determine and adjust the ventilation pressure for the next respiratory cycle according to the ventilation pressure of the current respiratory cycle and the time deviation ratio.

[0116] Further, in an embodiment of the present invention, the system further includes:

[0117] A first remeasurement module for initial ventilation pressure, configured to, when a user resets a new target tidal volume, recalculate the initial ventilation pressure according to the new target tidal volume and respiratory mechanics parameters, and apply it to the pressure-controlled ventilation for the next respiratory cycle;

[0118] A second remeasurement module for initial ventilation pressure, configured to, when it is detected that the change rate of the current respiratory mechanics parameters exceeds a predetermined change rate range, recalculate the initial ventilation pressure according to the target tidal volume and the current respiratory mechanics parameters, and apply it to the pressure-controlled ventilation for the next respiratory cycle.

[0119] Further, in an embodiment of the present invention, the system further includes:

[0120] An accumulated deviation amount calculation and judgment module, configured to, in all respiratory cycles after the first respiratory cycle, calculate in real time the accumulated deviation amount between the actual tidal volume and the target tidal volume, and judge whether the accumulated deviation amount exceeds a preset deviation amount threshold;

[0121] A restart module, configured to, when the accumulated deviation amount calculation and judgment module determines that the accumulated deviation amount exceeds the preset deviation amount threshold, forcibly terminate the current respiratory cycle and trigger an alarm, and at the same time reset the ventilation pressure to the initial ventilation pressure and restart the tentative ventilation.

[0122] Further, in an embodiment of the present invention, the system further includes:

[0123] A change rate calculation and judgment module, configured to calculate the change rate of the pressure adjustment amount between the ventilation pressure adjusted to the next respiratory cycle and the ventilation pressure of the current respiratory cycle, and judge whether the change rate of the pressure adjustment amount exceeds a preset maximum change rate;

[0124] A fifth ventilation pressure adjustment module, configured to, when the change rate calculation and judgment module determines that the change rate of the pressure adjustment amount exceeds the preset maximum change rate, determine and adjust the ventilation pressure for the next respiratory cycle according to the ventilation pressure of the current respiratory cycle and the preset maximum change rate.

[0125] The ventilation control system of the medical device provided by the embodiment of the present invention has the same implementation principle and technical effects as those of the foregoing method embodiment. For a brief description, for the parts not mentioned in the device embodiment, reference may be made to the corresponding content in the foregoing method embodiment.

[0126] Embodiment III

[0127] On the other hand, the present invention further provides a medical device. Please refer to Figure 3 , which shows the medical device in the third embodiment of the present invention, including a memory 20, a processor 10, and a program 30 stored on the memory 20 and executable on the processor. When the processor 10 executes the program 30, it implements the medical device ventilation control method as described in the above embodiments.

[0128] Among them, in some embodiments, the processor 10 may be a central processing unit (CPU), a controller, a microcontroller, a microprocessor, or other data processing chips, and is used to run the program code stored in the memory 20 or process data, such as executing an access restriction program, etc.

[0129] Among them, the memory 20 includes at least one type of readable storage medium. The readable storage medium includes flash memory, hard disk, multimedia card, card-type memory (such as SD or DX memory, etc.), magnetic memory, magnetic disk, optical disc, etc. In some embodiments, the memory 20 may be an internal storage unit of the medical device, such as the hard disk of the medical device. In other embodiments, the memory 20 may also be an external storage device of the medical device, such as a smart media card (SMC), secure digital (SD) card, flash card, etc. equipped on the medical device. Further, the memory 20 may also include both the internal storage unit and the external storage device of the medical device. The memory 20 can be used not only to store application software and various types of data installed on the medical device, but also to temporarily store data that has been output or will be output.

[0130] It should be noted that Figure 3 the shown structure does not constitute a limitation on the medical device. In other embodiments, the medical device may include fewer or more components than shown, or combine certain components, or have different component arrangements.

[0131] In summary, for the medical device in the above embodiments of the present invention, by calculating the initial ventilation pressure based on the target tidal volume set by the user and the respiratory mechanics parameters measured by tentative ventilation and applying it to the first respiratory cycle, it is possible to set an appropriate initial pressure according to the actual respiratory mechanics of the individual, avoiding the problems of excessive or insufficient initial pressure that may occur in traditional ventilation pressure setting, and thus achieving more accurate tidal volume control; by real-time monitoring the actual tidal volume of each respiratory cycle and determining whether the target tidal volume is reached within the preset target inhalation time, and if the actual inhalation time is less than the target inhalation time, the ventilation flow rate is immediately terminated and the inhalation pause phase is entered, so that the actual tidal volume is maintained at the target tidal volume without ventilation, avoiding the problem of tidal volume overshoot caused by excessive ventilation pressure, and adjusting the ventilation pressure of the next respiratory cycle according to the difference between the actual tidal volume and the target tidal volume. This dynamic adjustment mechanism enables the medical device to continuously optimize the ventilation pressure according to the feedback of each respiratory cycle, avoiding tidal volume deviation caused by the adjustment of the target tidal volume or drastic changes in the patient's respiratory mechanics parameters, and solving the problem of tidal volume overshoot that may occur under the existing pressure adjustment mechanism.

[0132] An embodiment of the present invention further provides a storage medium, on which a program is stored, and when the program is executed by a processor, it implements the medical device ventilation control method as described in the above embodiments.

[0133] Those skilled in the art can clearly understand that for the convenience and simplicity of description, only the above division of each functional unit and module is used as an example. In actual applications, the above functions can be allocated to different functional units or modules according to needs, that is, the internal structure of the storage device is divided into different functional units or modules to complete all or part of the functions described above. Each functional unit and module in the embodiments can be integrated into one processing unit, or each unit can exist physically alone, or two or more units can be integrated into one unit. The above integrated unit can be implemented in the form of hardware or in the form of a software functional unit. In addition, the specific names of each functional unit and module are only for the convenience of mutual distinction and do not limit the protection scope of the present application.

[0134] Those skilled in the art will understand that the logic and / or steps represented in the flowchart or otherwise described herein, for example, can be considered as a definite sequence list of executable instructions for implementing logical functions, and can be specifically implemented in any storage medium for use by an instruction execution system, apparatus, or device (such as a computer-based system, a system including a processor, or other systems that can fetch and execute instructions from the instruction execution system, apparatus, or device), or used in combination with these instruction execution systems, apparatus, or devices. For the purposes of this specification, a "storage medium" can be any device that can contain, store, communicate, propagate, or transport a program for use by or in combination with an instruction execution system, apparatus, or device.

[0135] More specific examples of storage media (a non-exhaustive list) include the following: an electrical connection part with one or more wirings (electronic device), a portable computer disk cartridge (magnetic device), a random access memory (RAM), a read-only memory (ROM), an erasable programmable read-only memory (EPROM or flash memory), an optical fiber device, and a portable compact disc read-only memory (CDROM). Additionally, the storage medium can even be paper or other suitable media on which the program can be printed, because the program can be obtained electronically, for example, by optically scanning the paper or other media, followed by editing, interpretation, or other suitable processing as necessary, and then stored in a memory.

[0136] It should be understood that various parts of the present invention can be implemented by hardware, software, firmware, or a combination thereof. In the above embodiments, multiple steps or methods can be implemented by software or firmware stored in a memory and executed by a suitable instruction execution system. For example, if implemented by hardware, as in another embodiment, any one or a combination of the following techniques well known in the art can be used: discrete logic circuits with logic gate circuits for implementing logical functions on data signals, application-specific integrated circuits with suitable combinational logic gate circuits, programmable gate arrays (PGAs), field-programmable gate arrays (FPGAs), etc.

[0137] In the description of this specification, the description with reference to terms such as "one embodiment", "some embodiments", "example", "specific example", or "some examples", etc. means that the specific features, structures, materials, or characteristics described in connection with the embodiment or example are included in at least one embodiment or example of the present invention. In this specification, the schematic representations of the above terms do not necessarily refer to the same embodiment or example. Moreover, the specific features, structures, materials, or characteristics described can be combined in a suitable manner in any one or more embodiments or examples.

[0138] The above-described embodiments merely represent several implementation manners of the present invention. The description thereof is relatively specific and detailed, but it should not be construed as a limitation to the scope of the present invention. It should be noted that for those of ordinary skill in the art, without departing from the concept of the present invention, several modifications and improvements can still be made, and these all fall within the protection scope of the present invention. Therefore, the protection scope of the present invention shall be subject to the appended claims.

Claims

1. A ventilation control system for medical equipment, characterized in that: Applied to medical equipment, the system comprises: An initial ventilation pressure calculation module is used to calculate the initial ventilation pressure based on the target tidal volume set by the user and the respiratory mechanics parameters determined by the trial ventilation, and apply it to the pressure-controlled ventilation in the first respiratory cycle; The tidal volume monitoring and judgment module is used to monitor the actual tidal volume of each respiratory cycle in real time and judge whether the target tidal volume is reached within the preset target inspiratory time; A first ventilation pressure adjustment module, configured to adjust the ventilation pressure of the next respiratory cycle according to the actual tidal volume and the target tidal volume if the target tidal volume is not reached within the target inspiratory time; An inspiratory time judgment module is used to judge whether the actual inspiratory time is less than the target inspiratory time if the target tidal volume is reached within the target inspiratory time; The second ventilation pressure adjustment module is used to immediately terminate the ventilation flow rate and enter the inspiratory pause stage when the inspiratory time judgment module judges that the actual inspiratory time is less than the target inspiratory time, and dynamically adjust the ventilation pressure of the next respiratory cycle according to the actual inspiratory time and the target inspiratory time of each respiratory cycle until the actual inspiratory time is equal to the target inspiratory time; The second ventilation pressure adjustment module comprises: A time deviation ratio calculation unit, used for calculating the time deviation ratio between the actual inspiratory time and the target inspiratory time; A second ventilation pressure adjustment unit, for determining and adjusting the ventilation pressure of the next respiratory cycle according to a preset adjustment coefficient of the ventilation pressure of the current respiratory cycle when the time deviation ratio is greater than the first deviation ratio; A third ventilation pressure adjustment unit, used for determining and adjusting the ventilation pressure of the next respiratory cycle according to the ventilation pressure of the current respiratory cycle and a preset pressure step when the time deviation ratio is less than the second deviation ratio; The fourth ventilation pressure adjustment unit is used to determine and adjust the ventilation pressure of the next respiratory cycle according to the ventilation pressure of the current respiratory cycle and the time deviation ratio when the time deviation ratio is less than the first deviation ratio and greater than the second deviation ratio.

2. A storage medium storing a program, characterized in that: When the program is executed by a processor, a ventilation control method for medical equipment is implemented. The ventilation control method for medical equipment is applied to a medical equipment, and the method includes: Based on the target tidal volume set by the user and the respiratory mechanics parameters determined by trial ventilation, the initial ventilation pressure is calculated and applied to the pressure-controlled ventilation in the first respiratory cycle; Monitor the actual tidal volume of each respiratory cycle in real time and determine whether the target tidal volume is reached within the preset target inspiratory time; If the target tidal volume is not reached within the target inspiratory time, the ventilation pressure of the next respiratory cycle is adjusted according to the actual tidal volume and the target tidal volume; If the target tidal volume is reached within the target inspiratory time, it is determined whether the actual inspiratory time is less than the target inspiratory time; If yes, the ventilation flow rate is immediately terminated and the patient enters the inspiratory pause phase. The ventilation pressure of the next respiratory cycle is dynamically adjusted according to the actual inspiratory time and the target inspiratory time of each respiratory cycle until the actual inspiratory time is equal to the target inspiratory time. The step of dynamically adjusting the ventilation pressure of the next respiratory cycle according to the actual inspiratory time and the target inspiratory time of each respiratory cycle comprises: Calculate the time deviation ratio between the actual inspiratory time and the target inspiratory time; When the time deviation ratio is greater than the first deviation ratio, the ventilation pressure of the next respiratory cycle is determined and adjusted according to the preset adjustment coefficient of the ventilation pressure of the current respiratory cycle; When the time deviation ratio is less than the second deviation ratio, the ventilation pressure of the next breathing cycle is determined and adjusted according to the ventilation pressure of the current breathing cycle and the preset pressure step; When the time deviation ratio is less than the first deviation ratio and greater than the second deviation ratio, the ventilation pressure of the next respiratory cycle is determined and adjusted according to the ventilation pressure of the current respiratory cycle and the time deviation ratio.

3. The storage medium according to claim 2, characterized in that The step of calculating the initial ventilation pressure based on the target tidal volume set by the user and the respiratory mechanics parameters measured by the trial ventilation and applying the initial ventilation pressure to the pressure-controlled ventilation in the first respiratory cycle includes: During the exploratory ventilation phase, a test flow was delivered at a constant test pressure, and the actual tidal volume, plateau pressure, peak inspiratory pressure, positive end-expiratory pressure, and peak inspiratory flow rate were monitored; The lung compliance in the respiratory mechanics parameters is calculated based on the actual tidal volume, plateau pressure, and positive end-expiratory pressure of ventilation; The airway resistance in the respiratory mechanics parameters is calculated based on the ventilation peak inspiratory pressure, platform pressure, and peak inspiratory flow rate; The initial ventilation pressure is calculated based on the target tidal volume, lung compliance, airway resistance, peak inspiratory flow rate and positive end-expiratory pressure set by the user; Pressure controlled ventilation with initial ventilation pressure loaded into the first respiratory cycle.

4. The storage medium according to claim 2, characterized in that The step of adjusting the ventilation pressure of the next respiratory cycle according to the actual tidal volume and the target tidal volume comprises: Calculate the tidal volume deviation between the actual tidal volume and the target tidal volume; The ventilation pressure of the next respiratory cycle is calculated and adjusted according to the ventilation pressure, tidal volume deviation value and lung compliance adjustment coefficient of the current respiratory cycle.

5. The storage medium according to claim 2, characterized in that The method further comprises: When the user resets the new target tidal volume, the initial ventilation pressure is recalculated according to the new target tidal volume and respiratory mechanics parameters, and applied to the pressure-controlled ventilation of the next respiratory cycle; or When it is detected that the change rate of the current respiratory mechanics parameter exceeds the predetermined change rate range, the initial ventilation pressure is recalculated according to the target tidal volume and the current respiratory mechanics parameter and applied to the pressure-controlled ventilation of the next respiratory cycle.

6. The storage medium according to claim 2, characterized in that The method further comprises: In all breathing cycles after the first breathing cycle, the cumulative deviation between the actual tidal volume and the target tidal volume is calculated in real time, and it is determined whether the cumulative deviation exceeds a preset deviation threshold; If so, the current breathing cycle is forcibly terminated and an alarm is triggered. At the same time, the ventilation pressure is reset to the initial ventilation pressure and tentative ventilation is restarted.

7. The storage medium according to claim 2, characterized in that The method further comprises: Calculating the rate of change of the pressure adjustment amount between the ventilation pressure adjusted to the next respiratory cycle and the ventilation pressure of the current respiratory cycle, and determining whether the rate of change of the pressure adjustment amount exceeds a preset maximum rate of change; If so, the ventilation pressure of the next respiratory cycle is determined and adjusted according to the ventilation pressure of the current respiratory cycle and the preset maximum change rate.

8. A medical device, characterized in that: The invention comprises a memory, a processor and a program stored in the memory and executable on the processor, wherein when the processor executes the program, a ventilation control method for a medical device is implemented, and the method comprises: Based on the target tidal volume set by the user and the respiratory mechanics parameters measured by trial ventilation, the initial ventilation pressure is calculated and applied to the pressure-controlled ventilation in the first respiratory cycle; Monitor the actual tidal volume of each respiratory cycle in real time and determine whether the target tidal volume is reached within the preset target inspiratory time; If the target tidal volume is not reached within the target inspiratory time, the ventilation pressure of the next respiratory cycle is adjusted according to the actual tidal volume and the target tidal volume; If the target tidal volume is reached within the target inspiratory time, it is determined whether the actual inspiratory time is less than the target inspiratory time; If yes, the ventilation flow rate is immediately terminated and the patient enters the inspiratory pause phase. The ventilation pressure of the next respiratory cycle is dynamically adjusted according to the actual inspiratory time and the target inspiratory time of each respiratory cycle until the actual inspiratory time is equal to the target inspiratory time. The step of dynamically adjusting the ventilation pressure of the next respiratory cycle according to the actual inspiratory time and the target inspiratory time of each respiratory cycle comprises: Calculate the time deviation ratio between the actual inspiratory time and the target inspiratory time; When the time deviation ratio is greater than the first deviation ratio, the ventilation pressure of the next respiratory cycle is determined and adjusted according to the preset adjustment coefficient of the ventilation pressure of the current respiratory cycle; When the time deviation ratio is less than the second deviation ratio, the ventilation pressure of the next breathing cycle is determined and adjusted according to the ventilation pressure of the current breathing cycle and the preset pressure step; When the time deviation ratio is less than the first deviation ratio and greater than the second deviation ratio, the ventilation pressure of the next respiratory cycle is determined and adjusted according to the ventilation pressure of the current respiratory cycle and the time deviation ratio.

9. The medical device according to claim 8, characterized in that The step of calculating the initial ventilation pressure based on the target tidal volume set by the user and the respiratory mechanics parameters measured by the trial ventilation and applying the initial ventilation pressure to the pressure-controlled ventilation in the first respiratory cycle includes: During the exploratory ventilation phase, a test flow was delivered at a constant test pressure, and the actual tidal volume, plateau pressure, peak inspiratory pressure, positive end-expiratory pressure, and peak inspiratory flow rate were monitored; The lung compliance in the respiratory mechanics parameters is calculated based on the actual tidal volume, plateau pressure, and positive end-expiratory pressure of ventilation; The airway resistance in the respiratory mechanics parameters is calculated based on the ventilation peak inspiratory pressure, platform pressure, and peak inspiratory flow rate; The initial ventilation pressure is calculated based on the target tidal volume, lung compliance, airway resistance, peak inspiratory flow rate and positive end-expiratory pressure set by the user; Pressure controlled ventilation with initial ventilation pressure loaded into the first respiratory cycle.

10. The medical device according to claim 8, characterized in that The step of adjusting the ventilation pressure of the next respiratory cycle according to the actual tidal volume and the target tidal volume comprises: Calculate the tidal volume deviation between the actual tidal volume and the target tidal volume; The ventilation pressure of the next respiratory cycle is calculated and adjusted according to the ventilation pressure, tidal volume deviation value and lung compliance adjustment coefficient of the current respiratory cycle.

11. The medical device according to claim 8, characterized in that The method further comprises: When the user resets the new target tidal volume, the initial ventilation pressure is recalculated according to the new target tidal volume and respiratory mechanics parameters, and applied to the pressure-controlled ventilation of the next respiratory cycle; or When it is detected that the change rate of the current respiratory mechanics parameter exceeds the predetermined change rate range, the initial ventilation pressure is recalculated according to the target tidal volume and the current respiratory mechanics parameter and applied to the pressure-controlled ventilation of the next respiratory cycle.

12. The medical device according to claim 8, characterized in that The method further comprises: In all breathing cycles after the first breathing cycle, the cumulative deviation between the actual tidal volume and the target tidal volume is calculated in real time, and it is determined whether the cumulative deviation exceeds a preset deviation threshold; If so, the current breathing cycle is forcibly terminated and an alarm is triggered. At the same time, the ventilation pressure is reset to the initial ventilation pressure and tentative ventilation is restarted.

13. The medical device according to claim 8, characterized in that The method further comprises: Calculating the rate of change of the pressure adjustment amount between the ventilation pressure adjusted to the next respiratory cycle and the ventilation pressure of the current respiratory cycle, and determining whether the rate of change of the pressure adjustment amount exceeds a preset maximum rate of change; If so, the ventilation pressure of the next respiratory cycle is determined and adjusted according to the ventilation pressure of the current respiratory cycle and the preset maximum change rate.

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