A method and device for automated control of anti-phase synchronous respiratory assistance

Abstract

This invention discloses an automated control method and device for reverse-phase synchronous respiratory assistance. The method involves receiving respiratory signals from a respiratory monitor while simultaneously tracking the intra-bag pressure data of a chest inflation / deflation cuff in real time. It obtains the intra-bag pressure change pattern during a single breath and uses this pattern to provide reverse-phase synchronous respiratory assistance. Alternatively, it analyzes the rotation time, direction, and speed of the inflation / deflation motor over time using this pattern and provides reverse-phase synchronous respiratory assistance according to the motor's movement. The device includes a respiratory monitor, a chest inflation / deflation cuff (the inflation process corresponds to the patient's exhalation, and the deflation process corresponds to the patient's inhalation), an intra-bag pressure monitoring structure for real-time monitoring of the cuff pressure, an inflation / deflation motor for inflating and deflation of the cuff, and a control device for reverse-phase respiratory assistance. Using this reverse-phase respiratory assistance device avoids the need for real-time monitoring during the respiratory process, allowing conscious patients to communicate and eat normally.

Description

Technical Field

[0001] This invention belongs to the field of respiratory assist device technology, specifically relating to respiratory assist devices that use a repeatedly inflatable and deflated gas device placed on the chest, and more specifically to an automated controlled method and device for anti-phase synchronous respiratory assistance. Background Technology

[0002] When patients with respiratory diseases experience severe dyspnea, their own ventilation capacity is insufficient to meet the body's needs, leading to hypoxia and carbon dioxide retention. Dyspnea can manifest as restrictive or obstructive. Diseases primarily characterized by obstructive dyspnea, such as chronic obstructive emphysema, are characterized by a decrease in forced expiratory volume in one second (FEV1), an increase in functional residual capacity (FRC), and significant carbon dioxide retention in blood gas analysis.

[0003] When medication is insufficient to resolve airway obstruction, patients require mechanical ventilation. Mechanical ventilation uses mechanical devices to generate gas at specific pressures, flow rates, and oxygen concentrations to assist the patient's breathing, thereby alleviating respiratory distress and improving hypoxia and carbon dioxide retention. Currently, the mainstream mechanical ventilation technique is positive pressure trans-airway ventilation (PPV): the patient's airway is connected to a mechanical ventilation device (ventilator), which generates pressure and actively delivers gas into the patient's airway and lungs. While PPV provides strong respiratory support, its implementation requires high patient cooperation and may even necessitate the use of sedatives and analgesics, often requiring an intensive care environment. This has led to the development of methods that assist breathing through chest compressions, such as 201510289811.2, a wearable external chest compression ventilator synchronized with the expiratory phase; and 201220512288.7, a non-invasive negative pressure electric ventilator. Chest compression-assisted ventilation provides less respiratory support than positive pressure ventilation (CPV), making it suitable for patients with some spontaneous breathing and consciousness. Its advantage lies in avoiding airway closure and improving patient compliance. However, current chest compression-assisted ventilation relies on real-time monitoring of breathing movements, requiring patients to minimize movement to ensure accurate monitoring. This monitoring method significantly restricts activity and causes anxiety in conscious patients, indirectly increasing medical costs. Therefore, a respiratory assist device that addresses these issues is needed, specifically an automated, counter-synchronous respiratory support method and device. Summary of the Invention

[0004] Currently, most wearable respiratory assist devices use an inflation / deflation structure placed on the chest. A wearable external chest compression ventilator synchronized with the expiratory phase (201510289811.2) has a scheme for monitoring respiratory rate using selective respiratory electromyography signals; however, this method is easily affected by the inherently mechanical control process, leading to inaccurate monitoring signals. Existing technology also includes nasal respiratory rate monitoring, but its purpose is only to obtain respiratory rate and respiratory phase to ensure real-time control of inflation / deflation. This is also achieved by simply opening and closing the deflation valve to adjust the cuff's inflation / deflation. Because nasal airflow monitoring instruments must always be positioned at the nostrils, mouth and lip movements during eating and communication can easily interfere with real-time respiratory monitoring, resulting in poor real-time tracking. In clinical practice, many patients using wearable assistive devices for assisted breathing have self-awareness and require eating and communication. When real-time respiratory monitoring is required to control assistive devices, regardless of whether electromyography, impedance analysis, respiratory motion monitoring, or nasal airflow monitoring is used, the patient must remain in a stable resting state to minimize monitoring interference. These methods of real-time respiratory monitoring limit the application scenarios of respiratory assistive devices and impose restrictions on patient activity and significant psychological stress.

[0005] This application discloses a method for reverse-phase synchronous respiratory assistance. It utilizes a respiratory monitoring structure to monitor several respiratory cycles, obtaining the average duration of each exhalation and inhalation. During respiratory monitoring, it simultaneously tracks the changes in intra-bag pressure during exhalation and inhalation of the chest cuff. The changes in cuff pressure during a single breath are then used to control inflation and deflation, using these cuff pressure variations to assist respiration. This method can obtain effective cuff pressure changes through only a few respiratory cycles during assisted respiration, replacing respiratory control with cuff pressure changes. This eliminates the need for real-time monitoring of respiration, saving the time and effort of constant attention. This allows conscious patients to eat and communicate normally without constantly checking the respiratory monitor, significantly reducing anxiety for both patients and caregivers during assisted respiration. The process does not use the direct respiratory rate to guide the inflation and deflation of the cuff. Instead, it uses the regular pressure changes inside the cuff during breathing to automatically control the reverse-phase ventilation assist. Because the cuff pressure is a data point that is not easily affected by the patient's activity, it is easy to implement the automatic control of the reverse-phase ventilation assist using this regularity. It is an automated reverse-phase synchronous ventilation assist device. There are no special requirements for real-time monitoring of the normal respiratory rate during the process. It is an effective way to control the reverse-phase ventilation assist by using the regularity of the reverse breathing phase.

[0006] This application also discloses an automated control device for anti-phase synchronous breathing assistance, which includes a respiratory monitor, a chest inflation / deflation bag, a bag pressure monitoring structure, and a control device.

[0007] The respiratory monitor tracks the entire respiratory cycle, including exhalation, inspiration, and the respiratory transition point. A chest cuff is inflated and deflated; inflation corresponds to the patient's exhalation, and deflation corresponds to the patient's inspiration. An intra-cuff pressure monitoring structure is connected to the cuff cavity to monitor the intra-cuff pressure in real time.

[0008] The control device receives respiratory signals from the respiratory monitor and acquires the exhalation process, inhalation process, and respiratory transition points of several respiratory cycles. During the exhalation process of several respiratory cycles, the chest inflation bag is inflated, and during the inhalation process, the chest inflation bag is deflated. During several respiratory cycles, the control device receives real-time tracking data of the intra-bag pressure of the chest inflation bag, so that the individual respiratory process and the intra-bag pressure change process have a time correspondence. The control device acquires the intra-bag pressure change pattern during an individual respiratory process, and uses the acquired intra-bag pressure change pattern to control the inflation and deflation process of the chest inflation bag to be inflated and deflated according to the intra-bag pressure change pattern during the individual respiratory process.

[0009] Furthermore, when monitoring the transition from expiration to inspiration, the highest intracavitary pressure of the cuff is recorded; when monitoring the transition from inspiration to expiration, the lowest intracavitary pressure of the cuff is recorded; simultaneously, the duration of expiration and inhalation are recorded, with the expiration duration corresponding to the inflation time of the cuff from the minimum to the maximum pressure value; and the inhalation duration corresponding to the deflation time of the cuff from the maximum to the minimum pressure value. After several respiratory cycles, the relationship between the respiratory transition point during a single respiratory process and the intracavitary pressure of the chest cuff, as well as the relationship between the respiratory duration and the duration of change in intracavitary pressure of the chest cuff, are obtained. The patterns of intracavitary pressure and the duration of change in intracavitary pressure of the chest cuff are used to provide anti-phase assisted breathing; alternatively, the maximum and minimum cuff pressure values ​​can be preset according to the patient's condition, and the expiration and inhalation durations are obtained through a respiratory monitor; and the pattern of cuff changes based on the expiration and inhalation durations is found; once the pattern is found, the respiratory monitor can be discontinued.

[0010] Alternatively, an external contact pressure monitoring structure can be installed between the chest inflation cuff 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 to the patient by the cuff.

[0011] The control device receives data from a nasal airflow monitor during exhalation and inhalation; presets the required extracorporeal contact pressure values ​​for each inhalation and exhalation; and, under the monitoring of the nasal airflow monitor, controls the inflation and deflation rates during exhalation and inhalation to ensure that the actual contact pressure value detected by the contact pressure detection structure matches the preset contact pressure value. Simultaneously, it records the intracorporeal pressure changes detected by the intracorporeal pressure detection structure during each exhalation and inhalation cycle. It then uses several respiratory cycles to obtain stable data on the intracorporeal pressure changes detected by the intracorporeal pressure detection structure during exhalation and inhalation. The control device controls the inflation and deflation of the chest inflator / deflation cuff according to the acquired intracorporeal pressure change patterns, with inflation corresponding to the patient's exhalation and deflation corresponding to the patient's inhalation. (Note: "several" refers to 3-10 respiratory cycles.)

[0012] Furthermore, an integrated inflation / deflation structure is designed, including an inflation / deflation motor. The motor rotates in different directions to achieve inflation and deflation. The control device controls the motor's rotation speed and direction based on the acquired intra-bag pressure changes to complete the inflation and deflation processes. This design ensures that the control device regulates the motor's rotation speed and direction according to the pattern of intra-bag pressure changes, making the entire process conform to the intra-bag pressure variation pattern. Even further, the rotation time, speed, and direction of the inflation / deflation motor over time are obtained using the intra-bag pressure variation pattern during a single breath. The control device controls the inflation / deflation motor to perform inflation / deflation actions according to these time and speed variations. This method not only eliminates the need for real-time monitoring, but also allows the entire respiratory control process to be independent of real-time monitoring of the intra-bag pressure. The entire process is adjusted solely by controlling the rotation time, direction, and speed of the inflation / deflation motor over time, providing a completely real-time-free reverse-phase respiratory control method and giving the patient a high degree of freedom during device use.

[0013] Furthermore, a breathing correction procedure is initiated once every preset cycle. The correction procedure follows the pattern of changes in intra-bag pressure during the initial breathing process, with each correction procedure consisting of 3-5 breathing cycles. This avoids problems caused by prolonged periods without correction, and the correction process is controlled within 20 seconds to avoid interfering with the patient.

[0014] Furthermore, the control device is equipped with a calibration reminder structure. When no signal is received from the respiratory monitor during the required calibration time, the calibration reminder structure sends a calibration signal to remind the respiratory monitor to be placed in a suitable position.

[0015] Furthermore, an abnormality reminder module is set up to ensure that assisted breathing force can be provided to the patient. Specifically, this is achieved through the reminder structure of the external contact pressure monitoring structure in conjunction with the control structure. When the external contact pressure monitoring structure cannot detect the preset pressure value, the reminder structure is triggered to alarm, or the breathing correction program is directly triggered.

[0016] Technical effect

[0017] By initially monitoring several respiratory cycles with a respiratory monitor and simultaneously tracking the intra-bag pressure of the chest inflation / deflation cuff, the respiratory process is correlated with changes in cuff pressure. This allows for the acquisition of a pattern of cuff pressure changes during a single breath, which guides the inflation / deflation of the chest cuff, ultimately providing reverse-phase respiratory assistance. Alternatively, the pattern of cuff pressure changes during a single breath can be used to obtain the rotation time, speed, and direction of the inflation / deflation motor over time. A control device then controls the inflation / deflation motor to perform inflation / deflation actions according to these time and speed / direction patterns, providing reverse-phase respiratory assistance. Both of these are automated reverse-phase respiratory assist devices with low reliance on real-time respiratory monitoring. Real-time tracking is only performed during the initial few breaths; once a pattern is established, reliance on respiratory monitoring is eliminated. Ultimately, this does not affect the patient's eating and communication if they are conscious, and the process does not require real-time monitoring of the respiratory process, greatly improving patient comfort and freedom, and reducing the workload for both patients and caregivers.

[0018] By setting up an external contact pressure monitoring structure, it is possible to ensure that the patient is given sufficient pressure for assisted exhalation, and to obtain data on the changes in intra-bag pressure in combination with the breathing process, so as to guide the subsequent inflation and deflation of the chest cuff and make the assisted exhalation force more sufficient.

[0019] By setting up an inflation and deflation structure with motors rotating in two directions, the inflation and deflation of the chest airbag can be made to follow the pressure change pattern inside the airbag.

[0020] By setting up the correction reminder program and the abnormality reminder module, it can be ensured that the patient is assisted in a normal breathing state, and correction can be made as soon as an abnormality occurs. Attached Figure Description

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

[0022] Figure 2 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 rear 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 longitudinal sectional view of the vest structure of the present invention;

[0027] Figure 7 This is a schematic diagram of the nasal breath airflow monitoring device of the present invention;

[0028] Explanation of main figure symbols

[0029] 1. Nasal airflow monitor; 11. Ear-hook structure; 12. Housing; 13. Guide section; 14. Nasal cavity section; 15. Airflow sensor; 2. Vest structure; 21. Strip-shaped airbag; 22. Inflation tube; 23. Inflation port; 24. Connecting fabric; 25. Through opening; 26. Velcro adjustment structure; 3. Intra-bag pressure monitoring structure; 4. Control device; 41. Calibration reminder structure; 5. Inflation / deflation structure; 6. Extra-bag contact pressure monitoring structure. Detailed Implementation

[0030] To make the objectives, technical solutions, and advantages of this application clearer, the technical solutions of this application will be clearly and completely described below in conjunction with specific embodiments and corresponding drawings. Obviously, the described embodiments are only a part of the embodiments of this application, and not all of them. Based on the embodiments in this application, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of this application.

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

[0032] To keep the drawings concise, only the parts relevant to this application are shown schematically in each drawing, and they do not represent the actual structure of the product. In addition, to make the drawings concise and easy to understand, in some drawings, only one of the components with the same structure or function is shown schematically, or only one of them is labeled.

[0033] In this document, unless otherwise expressly specified and limited, the terms "first" and "second" are used for descriptive purposes only and should not be construed as indicating or implying relative importance; unless otherwise specified or explained, the term "multiple" refers to two or more; the terms "connected," "fixed," etc., should be interpreted broadly. For example, "connected" can be a fixed connection, a detachable connection, an integral connection, or an electrical connection; it can be a direct connection or an indirect connection through an intermediate medium. Those skilled in the art can understand the specific meaning of the above terms in this application according to the specific circumstances.

[0034] An automated control device for reverse-phase synchronous breathing assistance includes a respiratory monitor, a chest inflation / deflation bag, 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, which is set in the patient's nasal cavity, is selected to monitor the relevant respiratory processes. The monitoring of the respiratory process is mainly carried out through an airflow sensor. When the airflow is detected to flow towards the outside of the nasal cavity, it is the exhalation process. Conversely, when the airflow is detected to flow into the nasal cavity, it is the inhalation process.

[0036] refer to Figure 7 The nasal airflow monitor 1 is an ear-hook structure 11, comprising an ear-hook structure, a housing 12 housing a micro battery and control board, a guide section 13, and a nasal cavity section 14; the nasal cavity section 14 houses an airflow sensor 15. This method allows the nasal airflow monitor 1 to be stably and effectively positioned in the nasal cavity without interference from other devices, enabling continuous wear or use only during the initial and calibration phases. The housing 12 is positioned in the corresponding area of ​​the face, ensuring that it is not affected by changes in patient position and does not cause discomfort. The guide section 13 provides a channel for the wire to pass through. In practice, the respiratory monitor can be operated using methods such as ventilator monitoring or other instruments capable of monitoring the respiratory process and respiratory transition points.

[0037] refer to Figure 2-6The chest inflation / deflation system features a wearable vest-like structure 2, with multiple strip-shaped airbags 21 positioned only at the chest location. Three inflation tubes 22 extend into each airbag. Each airbag has an inflation port 23. This design allows for communication between the multiple airbags via the inflation tubes 22, ensuring consistent intra-bag pressure. The multiple strip-shaped airbags 21 also guarantee uniform inflation and compression, preventing inflation in a small area. A connecting fabric 24 connects all the airbags 21, further ensuring uniform contact with the patient. The three inflation tubes 22 converge at the rear end to a main inflation tube 22, within which an intra-bag pressure monitoring structure 3 is installed. This structure communicates with the chest inflation / deflation system's cavity, allowing for real-time monitoring of the intra-bag pressure. Furthermore, multiple strip-shaped airbags 21 are positioned on one side of the vest corresponding to the chest area, with a through-opening 25 on the back of the vest. Adjustable Velcro structures 26 are located on both sides of the through-opening 25 to accommodate different patient body shapes. It should be noted that the vest structure 2 is made of non-elastic fabric; thus, when in use, the vest structure 2 is worn on the patient, and the Velcro is adjusted to ensure a tight fit, guaranteeing that inflation will create pressure to assist exhalation.

[0038] refer to Figure 1 The control device 4 receives respiratory signals from the respiratory monitor and acquires the exhalation process, inhalation process, and respiratory transition points for 3-10 respiratory cycles. During the exhalation process of 3-10 respiratory cycles, the chest inflation bag is inflated, and during the inhalation process, the chest inflation bag is deflated. During 3-10 respiratory cycles, the control device receives real-time tracking data of the intra-bag pressure of the chest inflation bag, so that the single respiratory process and the intra-bag pressure change process have a time correspondence. The control device acquires the intra-bag pressure change pattern during a single respiratory process and uses the acquired intra-bag pressure change pattern to control the chest inflation bag inflation and deflation process to be inflated and deflated according to the intra-bag pressure change pattern during the single respiratory process.

[0039] With the above-mentioned equipment setup, a nasal airflow monitor 1 placed in the patient's nasal cavity is used only for 3-10 respiratory cycles, with a maximum duration of 40 seconds. This brief respiratory monitoring method completes respiratory matching, and the patient only needs to ensure that the monitoring is effective. This process does not rely on real-time respiratory monitoring but utilizes the changes in intracavitary pressure during the respiratory process to provide inverse-phase assisted breathing, so that the entire respiratory process does not depend excessively on respiratory process monitoring.

[0040] One implementation method for tracking the intracavitary pressure changes during a single respiration is as follows: When the transition from expiration to inspiration is detected, the highest intracavitary pressure is recorded; when the transition from inspiration to expiration is detected, the lowest intracavitary pressure is recorded; simultaneously, the duration of expiration and the duration of inspiration are recorded, with the expiration duration corresponding to the inflation time of the intracavitary pressure from the minimum to the maximum pressure value; the duration of inspiration corresponds to the deflation time of the intracavitary pressure from the maximum to the minimum pressure value; after 3-8 respiratory cycles, the relationship between the respiratory transition point and the intracavitary pressure values ​​of the chest inflation / deflation bag, as well as the relationship between the respiratory duration and the duration of intracavitary pressure changes in the chest inflation / deflation bag, are obtained; finally, the intracavitary pressure values ​​of the chest inflation / deflation bag and the duration of intracavitary pressure changes in the chest inflation / deflation bag are used to perform counter-phase assisted breathing. Of course, the maximum and minimum balloon pressure values ​​can be preset according to the patient's condition. The respiratory monitor is used to obtain the duration of expiration and inhalation. The pattern of balloon changes based on the duration of expiration and inhalation can be found. Once the pattern is found, the respiratory monitor can be removed. In this way, the relationship between the respiratory transition point and the pressure inside the chest balloon, as well as the relationship between the duration of breathing and the duration of pressure changes inside the chest balloon, can be used to switch the breathing process. Ultimately, the effect of reverse assisted breathing can be achieved by using only the pressure inside the chest balloon and the duration of pressure changes. In this way, an effective pattern can be obtained in just 3-10 breathing cycles, and reverse assisted breathing can be achieved without the real-time tracking of the nasal airflow monitor.

[0041] Another implementation method for monitoring the pressure change within the bladder during a single breath is as follows: an external contact pressure monitoring structure 6 is set on the outside of the chest inflation bladder and on the connecting cloth 24, and multiple structures can be arrayed; 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 and inhalation processes from the nasal airflow monitor 1; presets the required extra-cavity contact pressure values ​​for the inhalation and exhalation processes; controls the inflation and deflation rates during the exhalation and inhalation processes 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; simultaneously records the intra-cavity pressure change data monitored by the intra-cavity pressure detection structure during the exhalation and inhalation processes of a single respiratory cycle; obtains stable intra-cavity pressure change pattern data monitored by the intra-cavity pressure detection structure during the exhalation and inhalation processes using 3-10 respiratory cycles; and controls the inflation and deflation of the chest inflation / deflation cuff according to the obtained intra-cavity 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. Ultimately, the aforementioned equipment setup allows the nasal airflow monitor 1 to operate for only 3-10 respiratory cycles, less than 40 seconds, to obtain a regular pattern of intra-bag pressure changes during respiration. This pattern is then used by the control device 4 to control the inflation / deflation structure 5 to complete the inflation / deflation process. This process allows patients and caregivers to relax when using the nasal airflow monitor 1 for respiratory monitoring, eliminating the need for constant monitoring and ensuring effective feeding and communication for patients with spontaneous breathing. For patients with stable breathing, 3-5 breaths are sufficient, while for patients with rapid breathing, 10 breaths are chosen to find a very stable breathing pattern, ensuring the effectiveness of subsequent reverse-phase assisted breathing. The specific number of breaths can be selected according to the individual patient's condition, but the main purpose remains to obtain the corresponding intra-bag pressure change pattern using a stable breathing pattern, thereby enabling reverse-phase assisted breathing. The application of this pattern is also analyzed using the control structure, with a motor assisting in achieving the desired intra-bag pressure change pattern.

[0042] An integrated inflation / deflation structure 5 is configured, comprising an inflation / deflation motor. The motor rotates in different directions to achieve inflation / deflation. A control device 4 controls the motor's rotation speed and direction based on the acquired intra-bag pressure variation to complete the inflation and deflation processes. This configuration ensures that the control device 4 regulates the motor's rotation speed and direction according to the pattern, making the entire process conform to the intra-bag pressure variation. A more preferred embodiment involves: utilizing the intra-bag pressure variation during a single breath to obtain the rotation time, speed, and direction of the inflation / deflation motor over time; the control device 4 controls the inflation / deflation motor to perform inflation / deflation actions according to these time and speed / direction variations, thereby achieving automated reverse-phase auxiliary control of the breathing process. The rotation directions of the motors corresponding to exhalation and inhalation are different. Analysis reveals the patterns of the inflation / deflation motor's rotation speed, direction, and time during a stable exhalation process, with the rotation time corresponding to the exhalation time; and the same patterns are found during inhalation, with the rotation time corresponding to the inhalation time. Ultimately, the control of breathing is transformed into the rhythmic inflation and deflation of the air-inflating and deflation motor. Control is achieved by adjusting the rotation speed, direction, and duration. This method offers a more independent approach to assisting breathing, reducing the need to focus solely on the intra-bag pressure and minimizing inaccurate pressure monitoring caused by patient movement. An inflatable / deflation motor with a brushless motor can be selected. Alternatively, one inflator and one deflation motor can be used, with the inflator controlling exhalation and the deflation motor controlling inhalation.

[0043] A more preferred implementation is as follows: To avoid excessive deviation between the assisted respiratory rate and the patient's spontaneous respiratory rate, a respiratory correction program is initiated every preset cycle. The correction program follows the pattern of intra-bag pressure changes during the initial respiratory process. For patients with stable breathing, the preset cycle is set to 20-30 minutes, with each correction program consisting of 3-5 respiratory cycles. For patients with rapid breathing, due to larger fluctuations in respiratory rate, the preset cycle is set to 5 minutes, with each correction program consisting of 8-10 respiratory cycles. By setting different preset cycles for different patients, patient safety can be ensured. Ultimately, this avoids problems caused by prolonged lack of correction, and the correction process is controlled within 20 seconds to avoid disturbing the patient.

[0044] A more preferred embodiment is as follows: a calibration reminder structure 41 is provided on the control device 4. When no signal is received from the respiratory monitor during the required calibration time, the calibration reminder structure 41 issues a calibration signal to remind the respiratory monitor to be placed in a suitable position. Specifically, it is a combination of a timer and a speaker structure. When the calibration time is reached, the speaker structure issues an alarm signal.

[0045] A more preferred implementation is to set an abnormality reminder function to ensure that the force of assisted breathing can be provided to the patient. Specifically, this is achieved by the reminder structure of the control structure in conjunction with the external contact pressure monitoring structure 6. When the external contact pressure monitoring structure 6 cannot detect the preset pressure value, the reminder structure is triggered to alarm, or the breathing correction program is directly triggered.

[0046] A more preferred embodiment is as follows: the control device 4 is equipped with a wireless signal transmission module, and the nasal airflow monitor 1 is equipped with a wireless signal transmission module, a micro battery, and a control board; the control board receives signals from the exhalation process, the inhalation process, and the breathing transition point; and transmits the signals to the control device 4 through the wireless signal transmission module. This arrangement avoids overly complex wiring in the device, separates the wiring for the head and chest, and prevents significant interference.

[0047] The specific operation flow of the automated reverse-phase assisted breathing implementation method is as follows: it is mainly for patients with stable breathing and respiratory monitoring using a nasal inhalation airflow monitor.

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

[0049] 2) Receive real-time tracking data of the intra-bladder pressure of the chest inflation / deflation bag during 3-5 respiratory cycles, so that the intra-bladder pressure change process of a single breathing process has a time correspondence, and obtain the change pattern of intra-bladder pressure during a single breathing process.

[0050] 3) By utilizing the changes in intracystic pressure during a single respiration, the rotation time, speed, and direction of the automatic inflation / deflation motor during a single respiration are analyzed and determined.

[0051] 4) By utilizing the rotation time, speed, and direction of the inflation / deflation motor during a single breathing process, the control device automatically controls the inflation / deflation motor to provide reverse-phase assisted breathing.

[0052] The entire process only requires about 20 seconds and monitoring of 3-5 respiratory cycles to convert the respiratory process into the pattern of intra-bag pressure change during a single respiratory process or the rotation time and rotation speed of a single respiratory process, as well as the pattern of rotation direction change over time. Finally, the control device 4 selects the above two patterns and controls the inflation and deflation motor to assist breathing in the opposite phase. There is no need to monitor the patient's breathing in real time during the process. Once a deviation occurs, the correction program is initiated. However, the correction program is short and has little impact on the patient.

[0053] The above description is merely a specific embodiment of this application. Under the guidance of the above teachings, those skilled in the art can make other improvements or modifications based on the above embodiments. Those skilled in the art should understand that the above specific description is only to better explain the purpose of this application, and the scope of protection of this application should be determined by the scope of the claims.

Claims

1. A device for independently controlled intermittent correction of reverse-phase respiratory assistance, suitable for patients with some spontaneous breathing and consciousness, comprising, A respiratory monitor tracks the entire respiratory cycle, including the exhalation process, the inhalation process, and the respiratory transition point. The respiratory monitor is a nasal airflow monitor, which is placed in the patient's nasal cavity; The chest airbag is inflated and deflated; the inflation process corresponds to the patient's exhalation process, and the deflation process corresponds to the patient's inhalation process. The intra-cavity pressure monitoring structure is connected to the cavity of the chest inflation balloon to monitor the pressure inside the cavity in real time. The control device (1) first receives the signal from the respiratory monitor and obtains the exhalation process, inhalation process and respiratory transition point of 3-10 respiratory cycles; the chest inflation bag is inflated during the exhalation process of 3-10 respiratory cycles, and the chest inflation bag is deflated during the inhalation process, and the data of the intra-bag pressure of the chest inflation bag is received in real time, so that the single respiratory process and the intra-bag pressure change process have time correspondence; when the exhalation to inhalation is detected, the highest intra-bag pressure is recorded; when the inhalation to exhalation is detected, the lowest intra-bag pressure is recorded; at the same time, the exhalation duration and the inhalation duration are recorded, the exhalation duration corresponds to the inflation time of the intra-bag pressure from the minimum pressure value to the maximum pressure value; the inhalation duration corresponds to the deflation time of the intra-bag pressure from the maximum pressure value to the minimum pressure value; through 3-10 respiratory cycles Then, the relationship between the breathing transition point and the high and low values ​​of the pressure inside the chest inflation and deflation bag during a single breathing process, and the relationship between the breathing duration and the duration of the pressure change inside the chest inflation and deflation bag, are obtained to obtain the pressure change pattern inside the bag during a single breathing process; (2) The control device uses the obtained pressure change pattern inside the bag during a single breathing process to independently control the inflation and deflation process of the chest inflation and deflation bag without the need for a respiratory monitor signal. It uses the high and low values ​​of the pressure inside the chest inflation and deflation bag and the duration of the pressure change pattern inside the chest inflation and deflation bag to provide reverse-phase assisted breathing; thereby avoiding the influence of the patient's diet, speech, and exercise on the nasal airflow, interfering with the working rhythm of the respiratory assist device, and ensuring the stability of the respiratory assist work; at the same time, the device does not need to monitor the breathing process in real time during operation, which greatly improves the patient's comfort and freedom. Alternatively, based on the patient's pulmonary function test results, the maximum and minimum intracystic pressure values ​​can be preset, and the duration of expiration and inhalation can be obtained through a respiratory monitor; based on the duration of expiration and inhalation, the pattern of intracystic pressure changes during a single respiratory process can be found for reverse-phase assisted ventilation; The control device is set to a calibration cycle, and the breathing calibration program is activated at regular intervals. The calibration program is performed according to the pattern of changes in intra-bag pressure during the initial breathing process, and each calibration program lasts for 3-10 breathing cycles. The calibration program setting allows the respiratory assist device to be dynamically adjusted according to the patient's movement status and ventilation needs. The control device is equipped with a calibration reminder structure. When a valid respiratory monitor signal is not received within the required calibration time, the calibration reminder structure sends a calibration signal to remind the user to check their spontaneous breathing status and place the respiratory monitor in the correct position, thereby improving the safety of the device.

2. The device according to claim 1, characterized in that, An external contact pressure monitoring structure is installed on the outside of the chest inflation bag to monitor the contact pressure with the chest during exhalation and inhalation. The control device receives data from the respiratory monitor during the exhalation and inhalation processes; presets the required extra-cavity contact pressure values ​​for the inhalation and exhalation processes; controls the inflation and deflation rates during exhalation and inhalation under the monitoring of the respiratory monitor to ensure that the actual contact pressure value detected by the contact pressure detection structure is the same as the preset contact pressure value; simultaneously records the intra-cavity pressure change data detected by the intra-cavity pressure detection structure during the exhalation and inhalation processes of a single respiratory cycle; acquires data on the intra-cavity pressure change pattern detected by the intra-cavity pressure detection structure during a single respiratory process using 3-10 respiratory cycles; and controls the inflation and deflation of the chest inflation / deflation cuff according to the acquired intra-cavity pressure change pattern.

3. The device according to claim 1, characterized in that, An integrated inflation / deflation structure is set up, which includes an inflation / deflation motor. The motor rotates in different directions to achieve inflation and deflation. The control device controls the rotation speed, rotation direction and corresponding time of the motor according to the obtained intra-bladder pressure change pattern to complete the inflation and deflation process.

4. The device according to claim 3, characterized in that, The rotation time, speed, and direction of the inflation / deflation motor during a single respiration are obtained by utilizing the change pattern of intracystic pressure. The control device controls the inflation / deflation motor to perform inflation / deflation actions according to the changes in rotation time, speed, and direction over time.

5. The device according to claim 1, characterized in that, An abnormality alert module is set up to ensure that assisted breathing force can be provided to the patient. The abnormality alert module includes an alert structure of the external contact pressure monitoring structure and the control device. When the external contact pressure monitoring structure fails to detect a preset pressure value, the alert structure is triggered to alarm, or the breathing correction program is directly triggered.

6. The device according to any one of claims 1-5, characterized in that, The nasal airflow monitor is an ear-hook type instrument, including an ear-hook structure, a housing with a micro battery and control board, a guide section and a nasal cavity section, and an airflow sensor installed in the nasal cavity section.

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