Automatically-controlled reverse phase synchronous breathing assistance method and equipment

Abstract

The invention discloses an automatic control antiphase synchronous breathing assistance method and equipment, and the method comprises the steps: receiving a breathing process signal of a breathing monitor, tracking in-bag pressure data of a chest inflation and deflation bag in real time, obtaining an in-bag pressure change rule in a single breathing process, and carrying out antiphase synchronous breathing assistance by utilizing the in-bag pressure change rule. Or the change rule of the rotation time, the rotation direction and the rotation speed of the inflation and deflation motor along with the time is obtained through analysis of the change rule of the pressure in the bag, and reverse-phase synchronous assisted respiration is conducted according to the rule of the inflation and deflation motor; the equipment comprises a respiration monitor and a chest inflation and deflation bag, the inflation process corresponds to the expiration process of a patient, the deflation process corresponds to the inspiration process of the patient, and an intra-bag pressure monitoring structure is used for monitoring intra-bag pressure in real time; the air bag is inflated and deflated through the inflation and deflation motor, the control device is used for conducting reverse-phase auxiliary respiration according to the method, real-time monitoring in the respiration process can be avoided through the reverse-phase respiration auxiliary equipment, and a patient with the independent consciousness can conduct normal language communication and diet.

Description

Technical Field

[0001] The present invention belongs to the technical field of respiratory assistance devices, and specifically relates to the field of respiratory assistance devices that are set on the chest and repeatedly inflate and discharge gas, and specifically provides an automatically controlled anti-phase synchronous respiratory assistance method and equipment. Background Art

[0002] When patients with respiratory diseases experience severe dyspnea, their own ventilation capacity cannot meet the body's needs, leading to hypoxia and carbon dioxide retention. Dyspnea can manifest as both restrictive and obstructive. Diseases characterized by obstructive dyspnea, such as chronic obstructive pulmonary emphysema, are characterized by decreased forced expiratory volume in 1 second, increased functional residual capacity, and significant carbon dioxide retention on blood gas analysis.

[0003] When medications are insufficient to resolve airway obstruction, patients require mechanical ventilation. Mechanical ventilation uses a mechanical device to generate gas at a specific pressure, flow rate, and oxygen concentration to assist the patient's breathing, thereby alleviating dyspnea and improving hypoxia and carbon dioxide retention. Currently, the mainstream mechanical ventilation technology is positive pressure ventilation: the patient's airway is connected to a mechanical ventilator (respirator), which generates a certain pressure and actively delivers gas into the patient's airway and lungs. While positive pressure ventilation can provide strong respiratory support, its implementation requires high patient cooperation and may even require the use of sedatives and analgesics, often requiring intensive care settings. Consequently, methods using pneumatic chest compressions to assist breathing have emerged, such as the wearable chest compression ventilator synchronized with the exhalation phase (201510289811.2) and the non-invasive negative pressure electric ventilator (201220512288.7). Chest compression-assisted technology does not provide as much respiratory support as positive pressure assisted ventilation through the airway. It is suitable for patients with a certain degree of spontaneous breathing and consciousness. Its advantage is that it avoids airway closure and improves patient compliance. However, the current chest compression-assisted technology for respiratory synchronization relies on real-time detection of respiratory movements, requiring patients to avoid movement as much as possible to ensure the accuracy of real-time monitoring. This monitoring method causes significant activity restrictions and mental anxiety for patients with autonomous consciousness, indirectly increasing medical costs. Therefore, there is a need for a respiratory assistance device that can solve the above problems, specifically a method and equipment for automatically controlled reverse-phase synchronous respiratory assistance. Summary of the Invention

[0004] Currently, wearable respiratory assistance devices mostly use an inflation and deflation mechanism mounted on the chest. (201510289811.2) A wearable chest compression ventilator synchronized with the exhalation phase has been proposed. Some approaches use respiratory myoelectric signals to monitor respiratory rate, but this approach is susceptible to interference from the inherently mechanically controlled process, which can lead to inaccurate monitoring signals. Other existing technologies monitor respiratory rate through the nasal cavity, but these are intended only to obtain respiratory rate and respiratory phase to ensure real-time respiratory monitoring to control inflation and deflation. Other approaches also adjust the inflation and deflation of the airbag by simply opening and closing the deflation valve. Because the nasal airflow monitoring device must always be positioned at the nostril, lip movements during eating, drinking, and communication can easily interfere with real-time respiratory monitoring, resulting in poor tracking. In clinical practice, many patients using wearable respiratory assistance devices are aware and have the need to eat and communicate. When real-time respiratory monitoring is required to control assistive devices, whether using electromyography, impedance analysis, respiratory movement monitoring, or nasal airflow monitoring, patients must remain in a stable resting state to minimize monitoring interference. These real-time respiratory monitoring methods limit the application scenarios of respiratory assistance devices and impose restrictions on patients' movements and significant mental stress.

[0005] The present application discloses a method for reverse synchronous respiratory assistance, which utilizes a respiratory monitoring structure to monitor several respiratory cycles, and utilizes multiple respiratory cycles to obtain the average duration of a single exhalation and inspiration. During respiratory monitoring, the variation pattern of the intra-sac pressure in the airbag during the exhalation and inspiration movements of the chest airbag is synchronously tracked, and then the variation pattern of the intra-sac pressure of the airbag during a single breath is utilized to perform the inflation and deflation movements, and the variation pattern of the intra-sac pressure in the airbag is utilized to assist breathing. This method can obtain an effective variation pattern of the intra-sac pressure in the airbag during the respiratory assistance process by only monitoring a few respiratory cycles, and replace the control of breathing with the variation pattern of the intra-sac pressure in the airbag; in this way, there is no need to track the respiratory situation in real time, and the process of paying attention to the respiratory monitoring in real time is omitted. This allows patients with autonomous consciousness to eat and communicate normally, and they do not need to pay attention to whether the respiratory monitor is in a normal monitoring state at any time, which greatly overcomes the anxiety of patients and caregivers during the assisted breathing process. The process does not use the direct respiratory frequency to guide the inflation and deflation of the airbag, but uses the regular pressure changes in the airbag during the breathing process to automatically control the reverse breathing assistance. Because the pressure in the airbag is a data that is not easily affected by the patient's activities, the method of automatically controlling the reverse breathing assistance using this law is easy to implement. It is an automated reverse-phase synchronous breathing assistance device. There are no special requirements for real-time monitoring of the normal respiratory frequency during the process. It is an effective way to control the reverse breathing assistance using the law of the reverse breathing phase.

[0006] The present application also discloses an automatically controlled inverse phase synchronous breathing assistance device, which includes a breathing monitor, a chest inflation and deflation air bag, an intra-bag pressure monitoring structure, and a control device.

[0007] The respiratory monitor monitors the entire respiratory cycle, including exhalation, inhalation, and respiratory transition points. The chest airbag inflates and deflates, with inflation corresponding to the patient's exhalation and deflation corresponding to their inhalation. An intra-bag pressure monitoring mechanism communicates with the chest airbag cavity, monitoring the intra-bag pressure in real time.

[0008] The control device receives the respiratory signal from the respiratory monitor to obtain the exhalation process, inhalation process and respiratory switching point of several respiratory cycles, inflates the chest airbag during the exhalation process of several respiratory cycles, and deflates the chest airbag during the inhalation process; receives the real-time tracked intra-bag pressure data of the chest airbag during several respiratory cycles, so that a single respiratory process and the intra-bag pressure change process have a time correspondence, obtains the intra-bag pressure change law during a single respiratory process, and uses the obtained intra-bag pressure change law during a single respiratory process to control the chest airbag inflation and deflation process to inflate and deflate according to the intra-bag pressure change law during the said single respiratory process.

[0009] Furthermore, when the transition from exhalation to inhalation is monitored, the highest intra-bag pressure of the airbag is recorded; when the transition from inhalation to exhalation is monitored, the lowest intra-bag pressure of the airbag is recorded; at the same time, the exhalation time and the inhalation time are recorded, the exhalation time corresponds to the inflation time of the airbag from the minimum pressure value to the maximum pressure value; the inhalation time corresponds to the deflation time of the airbag from the maximum pressure value to the minimum pressure value; after several breathing cycles, the relationship between the breathing switching point and the high and low values ​​of the intra-bag pressure of the chest inflation and deflation airbag in a single breathing process, and the relationship between the breathing time and the change time of the intra-bag pressure of the chest inflation and deflation airbag are obtained; the high and low values ​​of the intra-bag pressure of the chest inflation and deflation airbag and the change time of the high and low values ​​of the intra-bag pressure of the chest inflation and deflation airbag are used to reversely assist breathing; or the maximum and minimum bag pressure values ​​can be preset according to the patient's condition, and only the exhalation time and inhalation time are obtained through the respiratory monitor; and the change pattern of the bag is found based on the exhalation time and inhalation time; once the change pattern is found, it is no longer necessary to rely on the respiratory monitor.

[0010] Alternatively, an extra-bag contact pressure monitoring structure is provided, which is arranged between the chest inflation and deflation airbag and the patient's chest wall to monitor the contact pressure with the chest during exhalation and inhalation; this pressure is the auxiliary squeezing force applied by the airbag to the patient.

[0011] The control device receives the exhalation and inhalation processes acquired by the nasal airflow monitor; presets the external contact pressure values ​​required for the exhalation and inhalation processes; controls the inflation and deflation speeds during the exhalation and inhalation processes under the monitoring of the nasal airflow monitor so that the actual contact pressure values ​​detected by the contact pressure detection structure are the same as the preset contact pressure values; and simultaneously records the intra-sac pressure change data detected by the intra-sac pressure detection structure during the exhalation and inhalation processes of a single respiratory cycle; uses several respiratory cycles to obtain stable intra-sac pressure change pattern data detected by the intra-sac pressure detection structure during the exhalation and inhalation processes; the control device controls the inflation and deflation of the chest airbag according to the obtained intra-sac pressure change pattern, with the inflation process corresponding to the patient's exhalation process and the deflation process corresponding to the patient's inhalation process. The number to be specified refers to 3-10 respiratory processes.

[0012] Furthermore, an integrated inflation and deflation structure is provided, comprising an inflation and deflation motor, which rotates in different directions to achieve inflation and deflation. A control device controls the motor's rotational speed and direction based on the acquired intra-sac pressure variation pattern to complete the inflation and deflation processes. This arrangement ensures that the control device regulates the motor's rotational speed and direction according to the pattern, allowing the entire process to proceed in accordance with the intra-sac pressure variation pattern. Furthermore, the intra-sac pressure variation pattern during a single breath is utilized to obtain the rotation time, speed, and direction of the inflation and deflation motor over time. The control device controls the inflation and deflation motor to perform inflation and deflation actions in accordance with the rotation time, speed, and direction over time. This approach not only eliminates the influence of real-time monitoring, but also allows the entire breathing control process to be independent of the real-time monitoring of the chest inflation and deflation bag's intra-sac pressure. The entire process is adjusted solely by controlling the inflation and deflation motor's rotation time, direction, and speed over time. This represents a reverse breathing control method that is completely independent of real-time monitoring, allowing the patient a high degree of freedom during device use.

[0013] Furthermore, a breathing correction program is started once every preset period. The correction program is performed in accordance with the initial pattern of changes in the intra-sac pressure during breathing. Each correction program is performed for 3-5 breathing cycles to avoid problems caused by long-term non-calibration. In addition, the correction process is controlled within 20 seconds and will not interfere with the patient.

[0014] Furthermore, a correction reminder structure is provided on the control device. When no signal from the respiratory monitor is received within the required correction time, the correction reminder structure sends a correction signal to remind the user to place the respiratory monitor in a suitable position.

[0015] Furthermore, an abnormal reminder module is set up to ensure that assisted breathing force can be provided to the patient. This is specifically achieved through the reminder structure of the extra-sac contact pressure monitoring structure cooperating with the control structure. When the extra-sac contact pressure monitoring structure cannot monitor the preset pressure value, the reminder structure is triggered to alarm, or the breathing correction program is directly triggered.

[0016] Technical Effects

[0017] By initially monitoring several respiratory cycles using a respiratory monitor and synchronously tracking the intra-bag pressure of the chest inflation and deflation bag in real time, the respiratory process is made to correspond to the intra-bag pressure change, and the intra-bag pressure change pattern during a single breath is obtained. The obtained intra-bag pressure change pattern during a single breath is used to guide the inflation and deflation of the chest inflation and deflation bag, and finally complete the reverse phase assistance of breathing, or the change pattern of the intra-bag pressure during a single breath is used to obtain the rotation time, rotation speed and rotation direction of the inflation and deflation motor during a single breath; the control device controls the inflation and deflation motor to perform the inflation and deflation action according to the rotation time, rotation speed and rotation direction change pattern over time to complete the reverse phase assistance of breathing. Both of the above are automated reverse phase breathing assistance devices with low dependence on real-time respiratory monitoring. Real-time tracking is only performed during the initial few breaths. Once the pattern is determined, the dependence on respiratory monitoring can be eliminated, and ultimately the eating and communication of patients with independent consciousness is not affected. In addition, there is no need to monitor the respiratory process in real time during the process, which greatly improves the comfort and freedom of the patient and reduces the workload of the patient and the nursing staff.

[0018] By setting up an extra-bag contact pressure monitoring structure, we can ensure that the patient is given sufficient pressure to assist exhalation. Combined with the breathing process, we can obtain data on the regular changes in the pressure inside the bag, and guide the subsequent inflation and deflation actions of the chest air bag, making the assisted exhalation force more sufficient.

[0019] By providing an inflation and deflation structure with a motor rotating in two directions, the inflation and deflation of the chest airbag can be carried out completely in accordance with the law of changes in the pressure inside the bag.

[0020] By setting up the correction reminder program and the abnormal reminder module, it can be ensured that the patient is assisted in a normal breathing state and correction can be made once an abnormality occurs. BRIEF DESCRIPTION OF THE DRAWINGS

[0021] Figure 1 The reverse phase assisted breathing control process of the device of the present invention;

[0022] Figure 2 It is a schematic diagram of the overall structure of the invention;

[0023] Figure 3 This is a schematic diagram of the front view of the vest structure of the present invention;

[0024] Figure 4 This is a schematic diagram of the back view of the vest structure of the present invention;

[0025] Figure 5 This is a schematic diagram of the bottom view of the vest structure of the present invention;

[0026] Figure 6 This is a schematic diagram of the longitudinal cross-sectional structure of the vest structure of the present invention;

[0027] Figure 7 This is a schematic structural diagram of the nasal airflow monitor of the present invention;

[0028] Description of main reference numerals

[0029] 1. Nasal airflow monitor; 11. Ear-hanging structure; 12. Housing; 13. Guide part; 14. Nasal cavity; 15. Airflow sensor; 2. Vest structure; 21. Strip airbag; 22. Inflation tube; 23. Inflation hole; 24. Connecting cloth; 25. Through opening; 26. Velcro adjustment structure; 3. Intra-bag pressure monitoring structure; 4. Control device; 41. Calibration reminder structure; 5. Inflation and deflation structure; 6. External bag contact pressure monitoring structure. DETAILED DESCRIPTION

[0030] To make the purpose, technical solutions, and advantages of this application more clear, the following will provide a clear and complete description of the technical solutions of this application in conjunction with the specific embodiments of this application and the corresponding drawings. Obviously, the embodiments described are only part of the embodiments of this application, not all of them. Based on the embodiments in this application, all other embodiments obtained by ordinary technicians in this field without making creative efforts are within the scope of protection of this application.

[0031] In this document, “illustrative” means “serving as an example, instance or illustration”, and any diagram or implementation described in this document as “illustrative” should not be interpreted as a more preferred or more advantageous technical solution.

[0032] To simplify the drawings, only the parts related to the present application are schematically shown in each figure, and they do not represent the actual structure of the product. In addition, to simplify the drawings and facilitate understanding, in some figures, only one of the components with the same structure or function is schematically shown or labeled.

[0033] In this document, unless otherwise specified or limited, the terms "first" and "second" are used for descriptive purposes only and should not be understood to indicate or imply relative importance. Unless otherwise specified or explained, the term "plurality" refers to two or more. The terms "connected" and "fixed" should be understood broadly. For example, "connected" can mean a fixed connection, a detachable connection, an integral connection, or an electrical connection; it can be directly connected or indirectly connected through an intermediate medium. For those skilled in the art, the specific meanings of the above terms in this application can be understood according to specific circumstances.

[0034] An automatically controlled inverse phase synchronous respiratory assistance device comprises a respiratory monitor, a chest air bag for inflation and deflation, an intra-bag pressure monitoring structure 3, and a control device 4.

[0035] The respiratory monitor monitors the entire respiratory cycle, including the exhalation process, the inhalation process and the respiratory transition point; specifically, a nasal airflow monitor 1 is selected and set at the patient's nasal cavity to monitor the relevant respiratory process, mainly through the airflow sensor to monitor the respiratory process. When the airflow is detected flowing toward the outside of the nasal cavity, it is the exhalation process. On the contrary, when the airflow is detected flowing into the nasal cavity, it is the inhalation process.

[0036] refer to Figure 7 The nasal airflow monitor 1 is an ear-hanging structure 11, which includes an ear-hanging structure, a housing 12 for a microbattery and a control panel; a guide portion 13 and a nasal cavity portion 14; and an airflow receptor 15 is provided in the nasal cavity portion 14. In this way, the nasal airflow monitor 1 can be stably and effectively set to the nasal cavity position without being interfered with by other devices. It can be worn all the time, and can also be worn and used only in the initial and calibration stages. The housing 12 is set in the corresponding area of ​​the face. This setting can ensure that it is not affected by changes in the patient's body position when worn, and will not cause discomfort to the patient due to changes in body position. The guide portion 13 is provided with a channel that allows the wire to pass through. Of course, during the specific operation, the respiratory monitor can choose a method such as ventilator monitoring or other related instruments and equipment that can monitor the breathing process and breathing conversion points.

[0037] refer to Figure 2-6; The chest inflatable airbag, the inflation process corresponds to the patient's exhalation process, and the deflation process corresponds to the patient's inhalation process; the chest inflatable airbag is a wearable vest structure 2, which is only provided with multiple groups of strip airbags 21 at the chest position, and three inflation tubes 22 extending into each airbag; the inflation tubes 22 are provided with inflation holes 23 corresponding to the position of each airbag; this arrangement can achieve the connection of multiple airbags through the inflation tubes 22, ensuring the consistency of the intra-airbag pressure, and the arrangement of multiple groups of strip airbags 21 can ensure the uniformity of the inflation and extrusion effect, rather than inflating a single small area; a connecting cloth 24 is also provided on the multiple groups of strip airbags 21 to connect all the strip airbags 21; the provision of the connecting cloth 24 can further ensure the uniformity of the contact surface with the patient; the three inflation tubes 22 converge at the rear end to the main inflation tube 22, and an intra-airbag pressure monitoring structure 3 is provided in the main inflation tube 22; the intra-airbag pressure monitoring structure 3 is connected to the bladder cavity of the chest inflatable airbag to monitor the intra-airbag pressure in the bladder cavity in real time. Multiple strip-shaped airbags 21 are positioned on one side of the vest, corresponding to the chest area. A through-opening 25 is provided on the back of the vest, and Velcro adjustment structures 26 are positioned on either side of the through-opening 25 to accommodate the body shapes of different patients. It should be noted that the vest structure 2 is made of inelastic fabric. When in use, the vest structure 2 is placed on the patient and the Velcro is adjusted to fit the patient tightly, ensuring that inflation creates a pressure that assists exhalation.

[0038] refer to Figure 1 The control device 4 receives the respiratory signal of the respiratory monitor to obtain the exhalation process, the inhalation process and the respiratory transition point of 3-10 respiratory cycles, inflates the chest airbag during the exhalation process of 3-10 respiratory cycles, and deflates the chest airbag during the inhalation process; receives the real-time tracked intra-bag pressure data of the chest airbag during 3-10 respiratory cycles, so that a single respiratory process and the intra-bag pressure change process have a time correspondence, obtains the intra-bag pressure change law during a single respiratory process, and uses the obtained intra-bag pressure change law during a single respiratory process to control the chest airbag inflation and deflation process to inflate and deflate according to the intra-bag pressure change law during the single respiratory process.

[0039] With the above-mentioned device setup, the nasal airflow monitor 1, placed in the patient's nasal cavity, only requires 3-10 breathing cycles, with a maximum duration of 40 seconds. This is a short-term breathing monitoring method to complete respiratory matching, and the patient only needs to ensure effective acquisition. This process does not rely on real-time breathing process monitoring, but instead uses the law of changes in intra-sac pressure during breathing to reverse assist breathing, making the entire breathing process less dependent on breathing process monitoring.

[0040] An implementation method for the change law of the airbag pressure during a single breath is as follows: when monitoring the transition from exhalation to inhalation, the highest intra-bag pressure of the airbag is recorded; when monitoring the transition from inhalation to exhalation, the lowest intra-bag pressure of the airbag is recorded; at the same time, the exhalation time and the inhalation time are recorded, the exhalation time corresponds to the inflation time of the airbag pressure from the minimum pressure value to the maximum pressure value; the inhalation time corresponds to the deflation time of the airbag pressure from the maximum pressure value to the minimum pressure value; after 3-8 breathing cycles, the relationship between the breathing switching point and the high and low values ​​of the airbag pressure when the chest is inflated and deflated, and the relationship between the breathing time and the change time of the airbag pressure when the chest is inflated and deflated are obtained; finally, the high and low values ​​of the airbag pressure when the chest is inflated and deflated and the change time of the high and low values ​​of the airbag pressure when the chest is inflated and deflated are used to perform reverse assisted breathing. Of course, the maximum and minimum balloon pressure values ​​can also be preset according to the patient's condition, and the exhalation time and inhalation time are obtained through the respiratory monitor; and the change pattern of the balloon is found according to the exhalation time and inhalation time; once the change pattern is found, the respiratory monitor can be withdrawn. In this way, the relationship between the breathing conversion point and the high and low values ​​of the intra-bag pressure of the chest inflation and deflation airbag, and the relationship between the breathing time and the change time of the intra-bag pressure of the chest inflation and deflation airbag can be used to convert the breathing process, and finally the effect of reverse assisted breathing can be achieved by only using the high and low values ​​of the intra-bag pressure of the chest inflation and deflation airbag and the change time of the high and low values ​​of the intra-bag pressure of the chest inflation and deflation airbag. In this way, an effective pattern can be obtained through only 3-10 breathing cycles, and reverse assisted breathing can be achieved without the real-time tracking of the nasal airflow monitor 1.

[0041] Another implementation method for monitoring the law of changes in the pressure inside the bag during a single breath is to set up an extra-bag contact pressure monitoring structure 6, which is set on the outside of the chest inflation and deflation bag and on the connecting cloth 24, and can be arranged in an array; it is used to monitor the contact pressure with the chest during exhalation and inhalation; this pressure is used to monitor the auxiliary squeezing force applied to the patient. The control device 4 receives the exhalation process and the inhalation process obtained by the nasal airflow monitor 1; presets the preset extra-sac contact pressure value required for the inhalation process and the exhalation process, and controls the inflation and deflation speed during the exhalation and inhalation process under the monitoring of the nasal airflow monitor 1 so that the actual contact pressure value monitored by the contact pressure detection structure is the same as the preset contact pressure value, and at the same time records the intra-sac pressure change data monitored by the intra-sac pressure detection structure during the exhalation process and the inhalation process of a single breathing cycle; uses 3-10 breathing cycles to obtain the intra-sac pressure change law data monitored by the intra-sac pressure detection structure during the stable exhalation process and inhalation process; the control device 4 controls the inflation and deflation of the chest airbag according to the obtained intra-sac pressure change law, the inflation process corresponds to the patient's exhalation process, and the deflation process corresponds to the patient's inhalation process. Ultimately, the aforementioned device configuration allows the nasal airflow monitor 1 to operate for only 3-10 respiratory cycles, or less than 40 seconds of monitoring, to obtain the regular intra-sac pressure variation pattern required by the intra-sac pressure detection structure during a regular breathing process. This pattern is then used by the control device 4 to control the inflation / deflation mechanism 5 to complete the inflation / deflation action. This process allows the patient and caregiver to relax when using the nasal airflow monitor 1 for respiratory monitoring, eliminating the need to constantly monitor the device. This ensures that patients with spontaneous breathing awareness can effectively eat and communicate. For patients with stable breathing, 3-5 breaths are sufficient, while for those with rapid breathing, 10 breaths are sufficient to establish a stable breathing pattern, ensuring the effectiveness of subsequent reverse-phase breathing assistance. The specific number of breaths can also be selected based on the individual patient's condition, but the primary purpose remains to utilize a stable breathing pattern to obtain a corresponding intra-sac pressure variation pattern, thereby enabling reverse-phase breathing assistance. The application of this pattern is also analyzed using the control structure, with the motor cooperating to achieve the desired intra-sac pressure variation pattern.

[0042] A gas-inflating and deflation-integrated structure 5 is provided, comprising a gas-inflating and deflation-integrated motor. The motor rotates in different directions to achieve inflation and deflation. A control device 4 controls the motor's rotational speed and direction based on the acquired intra-sac pressure variation pattern to complete the inflation and deflation processes. This arrangement ensures that the control device 4 regulates the motor's rotational speed and direction according to a regular pattern, allowing the entire process to proceed in accordance with the intra-sac pressure variation pattern. A more preferred embodiment utilizes the intra-sac pressure variation pattern during a single breath to obtain the rotational time, speed, and direction of the gas-inflating and deflation motor over time. The control device 4 controls the gas-inflating and deflation motor to perform the inflation and deflation actions according to the temporal variations in rotational time, speed, and direction, thereby achieving automated reverse-phase auxiliary control of the respiratory process. The motor's rotational direction is different for exhalation and inhalation. Analysis reveals the regularity of the gas-inflating and deflation motor's rotational speed, direction, and time during a stable exhalation process, with the rotational time corresponding to the exhalation time. Furthermore, the regularity of the rotational speed, direction, and time during an inhalation process is determined, with the rotational time corresponding to the inhalation time. Ultimately, the control of the breathing action is converted into the regular inflation and deflation action of the inflation and deflation motor, which is controlled by controlling the rotation speed, rotation direction and rotation time. This method is a reverse breathing assistance method that is more independent of the focus on the intra-bag pressure, and can better reduce the occurrence of inaccurate intra-bag pressure monitoring of the chest inflation and deflation bag caused by patient activity. An inflatable and deflation motor with a brushless motor can be selected. Of course, in the specific implementation process, one inflation motor and one deflation motor can be selected, where the inflation motor controls the exhalation process and the deflation motor controls the inhalation process.

[0043] A more preferred embodiment is as follows: to avoid excessive deviation between the assisted breathing rate and the patient's spontaneous breathing rate, a breathing correction procedure is started every preset period, and the correction procedure is performed in accordance with the initial pattern of changes in the intra-sac pressure during the breathing process; for patients with stable breathing, the preset period is set to 20-30 minutes, and each correction procedure is performed for 3-5 breathing cycles; for patients with rapid breathing, whose breathing rate fluctuates greatly, the preset period is set to 5 minutes, and each correction procedure is performed for 8-10 breathing cycles; by setting different preset periods for different patients, the safety of the patients can be guaranteed. Ultimately, the problem of not correcting for a long time can be avoided, and the correction process is controlled within 20 seconds without disturbing the patient.

[0044] A more preferred embodiment is to provide a calibration reminder mechanism 41 on the control device 4. If no signal from the respiratory monitor is received within the required calibration time, the calibration reminder mechanism 41 issues a calibration signal to remind the user to properly position the respiratory monitor. Specifically, the mechanism comprises a timer and a speaker mechanism. When the calibration time is reached, the speaker mechanism issues an alarm signal.

[0045] A more preferred implementation is: setting an abnormal reminder function to ensure that the patient can be provided with auxiliary breathing force, which is specifically achieved through the extra-sac contact pressure monitoring structure 6 cooperating with the reminder structure of the control structure. When the extra-sac contact pressure monitoring structure 6 cannot monitor the preset pressure value; trigger the reminder structure alarm, or directly trigger the breathing correction program.

[0046] A more preferred embodiment is to configure the control device 4 with a wireless signal transmission module, and the nasal airflow monitor 1 with the wireless signal transmission module, a microbattery, and a control board. The control board receives signals from the exhalation process, the inhalation process, and the respiratory transition point, and transmits these signals to the control device 4 via the wireless signal transmission module. This configuration avoids excessive wiring complexity, separates the head and chest wiring, and minimizes significant interference.

[0047] The specific operating process of the implementation method of automated reverse-phase assisted breathing is to control the inflation and deflation motor by utilizing the rotation time and speed of a single breathing process, and the change pattern of the rotation direction over time. It is a control method mainly for patients with stable breathing and who choose a nasal airflow monitor for respiratory monitoring.

[0048] refer to Figure 1 ;1) Receive the signal from the nasal airflow monitor 1, obtain the exhalation process, inhalation process and respiratory transition point of 3-5 respiratory cycles, and track the intra-bag pressure of the chest airbag in real time during breathing.

[0049] 2) Receive real-time tracking of the chest airbag pressure data during inflation and deflation over 3-5 respiratory cycles, so that the individual breathing process and the change process of the airbag pressure have a temporal correspondence, and obtain the change pattern of the airbag pressure during a single breathing process.

[0050] 3) Using the obtained variation pattern of the intra-sac pressure during a single breath, the rotation time, rotation speed, and rotation direction of the automatic inflation and deflation motor during a single breath are analyzed and obtained.

[0051] 4) By utilizing the rotation time and rotation speed of the inflation and deflation motor in a single breathing process, and the change pattern of the rotation direction over time, the control device automatically controls the inflation and deflation motor to reversely assist breathing.

[0052] The entire process only requires monitoring of 3-5 breathing cycles for about 20 seconds to convert the breathing process into the law of changes in the pressure in the bag during a single breathing process or the rotation time and rotation speed of a single breathing process, and the law of changes in the rotation direction over time; finally, the control device 4 selects the above two laws to control the inflation and deflation motors to assist breathing in reverse. During the process, there is no need to monitor the patient's breathing in real time. Once there is a deviation, the correction program will be started here, but the correction program is short and has little impact on the patient.

[0053] The above description is only a specific embodiment of the present application. Based on the above teachings of the present application, those skilled in the art may make other improvements or modifications based on the above embodiments. Those skilled in the art should understand that the above description is only a better explanation of the purpose of the present application, and the scope of protection of the present application shall be based on the scope of protection of the claims.

Claims

1. A reverse phase synchronous breathing assistance method, characterized in that: S1, receiving respiratory signals from a respiratory monitor to obtain the exhalation process, inspiration process, and respiratory transition points of several respiratory cycles, inflating the chest airbag during the exhalation process of several respiratory cycles, and deflating the chest airbag during the inspiration process, and tracking the intra-bag pressure of the chest airbag in real time during the breathing process; S2, receiving real-time tracked chest airbag pressure data during inflation and deflation over several respiratory cycles, so that a single respiratory process and the change process of the airbag pressure have a temporal correspondence, and obtaining the change pattern of the airbag pressure during a single respiratory process; S3, using the acquired intra-sac pressure variation pattern during a single breath, controlling the chest airbag inflation and deflation process to inflate and deflate according to the intra-sac pressure variation pattern during the single breath; Alternatively, S3, the inflation and deflation are controlled by the inflation and deflation motor, and the variation pattern of the pressure inside the bag during a single breathing process is obtained to analyze and obtain the variation pattern of the rotation time, rotation speed, and rotation direction of the automatic inflation and deflation motor during a single breathing process; S4, the inflation and deflation motor is automatically controlled to reversely assist breathing by utilizing the variation pattern of the rotation time, rotation speed, and rotation direction of the inflation and deflation motor during a single breathing process.

2. An automatically controlled inverse phase synchronous respiratory assistance device, comprising: Respiratory monitor, which monitors the entire respiratory cycle, including exhalation, inhalation, and respiratory transition points; The chest air bag is inflated and deflated, with the inflation process corresponding to the patient's exhalation process and the deflation process corresponding to the patient's inhalation process; The intra-sac pressure monitoring structure is connected to the sac cavity of the chest airbag and monitors the intra-sac pressure in the sac cavity in real time; it is characterized by further comprising: The control device receives the respiratory signal of the respiratory monitor and obtains the exhalation process, the inhalation process and the respiratory switching point of several respiratory cycles, inflates the chest air bag during the exhalation process of several respiratory cycles, and deflates the chest air bag during the inhalation process; receives the real-time tracked intra-bag pressure data of the chest air bag during several respiratory cycles, so that a single respiratory process and the intra-bag pressure change process have a time correspondence, obtains the intra-bag pressure change law during a single respiratory process, and uses the obtained intra-bag pressure change law during a single respiratory process to control the chest air bag inflation and deflation process to inflate and deflate according to the intra-bag pressure change law during the single respiratory process.

3. The device according to claim 2, characterized in that When monitoring the transition from exhalation to inhalation, record the highest intra-bag pressure of the airbag; when monitoring the transition from inhalation to exhalation, record the lowest intra-bag pressure of the airbag; at the same time, record the exhalation time and the inspiration time, the exhalation time corresponds to the inflation time of the airbag from the minimum pressure value to the maximum pressure value; the inspiration time corresponds to the deflation time of the airbag from the maximum pressure value to the minimum pressure value; after several breathing cycles, obtain the relationship between the breathing switching point and the high and low values ​​of the intra-bag pressure of the chest inflation and deflation airbag during a single breath, as well as the relationship between the breathing time and the duration of the change of the intra-bag pressure of the chest inflation and deflation airbag; use the high and low values ​​of the intra-bag pressure of the chest inflation and deflation airbag and the duration of the change of the high and low values ​​of the intra-bag pressure of the chest inflation and deflation airbag to reversely assist breathing; Alternatively, the maximum and minimum intra-sac pressure values ​​can be preset according to the patient's condition, and the exhalation and inhalation durations can be obtained through a respiratory monitor; based on the exhalation and inhalation durations, the changing duration pattern of the intra-sac pressure in a single breathing process can be found to perform reverse assisted breathing.

4. The device according to claim 2, characterized in that An external contact pressure monitoring structure is provided, which is arranged outside the chest airbag and is used to monitor the contact pressure with the chest during exhalation and inhalation; The control device receives the exhalation process and the inhalation process obtained by the respiratory monitor; presets the preset external airbag contact pressure values ​​required for the inhalation process and the exhalation process, controls the inflation and deflation speeds during the exhalation and inhalation processes under the monitoring of the respiratory monitor so that the actual contact pressure value monitored by the contact pressure detection structure is the same as the preset contact pressure value, and simultaneously records the intra-airbag pressure change data monitored by the intra-airbag pressure detection structure during the exhalation process and the inhalation process of a single breathing cycle; obtains the intra-airbag pressure change law data monitored by the intra-airbag pressure detection structure during a single breathing process using several breathing cycles; and the control device controls the inflation and deflation of the chest airbag according to the obtained intra-airbag pressure change law.

5. The device according to claim 2, characterized in that An integrated inflation and deflation structure is set up, which includes an inflation and deflation motor, and the motor rotates in different directions to achieve inflation and deflation; the control device controls the motor's rotation speed, rotation direction and corresponding time according to the acquired law of change of the intra-bag pressure to complete the inflation and deflation processes.

6. The device according to claim 5, characterized in that The change pattern of the pressure inside the bag during a single breath is used to obtain the rotation time of the inflation and deflation motor and the change pattern of the rotation speed and rotation direction over time during a single breath; the control device controls the inflation and deflation motor to perform inflation and deflation actions according to the change pattern of the rotation time and the rotation speed and rotation direction over time.

7. The device according to claim 2, characterized in that A preset cycle is set, and a breathing calibration program is started every preset cycle. The calibration program is performed in accordance with the initial method of obtaining the law of changes in the intra-sac pressure during the breathing process. Each calibration program is performed for several breathing cycles.

8. The device according to claim 7, characterized in that A calibration reminder structure is provided on the control device. When the signal from the respiratory monitor is not received within the required calibration time, the calibration reminder structure sends a calibration signal to remind the user to place the respiratory monitor in the correct position.

9. The device according to claim 7, characterized in that An abnormal reminder module is set up to ensure that assisted breathing force can be provided to the patient. The abnormal reminder module includes an extra-sac contact pressure monitoring structure and a reminder structure of the control device. When the extra-sac contact pressure monitoring structure fails to detect the preset pressure value, the reminder structure is triggered to alarm, or the breathing correction program is directly triggered.

10. The device according to any one of claims 2 to 9, characterized in that: The respiratory monitor is a nasal airflow monitor, which is installed in the patient's nasal cavity. The nasal airflow monitor is an ear-hanging instrument, including an ear-hanging structure, a shell with a micro battery and a control panel; a guide part and a nasal cavity part; and an airflow sensor is installed in the nasal cavity.

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