A breathing system for rapid conversion

Abstract

This invention relates to a respiratory system for rapid switching, comprising a delivery unit for providing gas to a patient; a monitoring unit for monitoring the gas flow rate and tidal volume; and a transfer unit for connecting the delivery unit to different gas sources. The monitoring unit monitors the gas flow information within the buffer chamber directly accessible to the patient by being installed between the buffer chamber and the regulating chamber of the delivery unit. A control unit disposed within the delivery unit adjusts the delivery unit based on the flow information acquired by the monitoring unit. The transfer unit connects the delivery unit to different gas sources by opening different connection channels according to preset rules, ensuring stable gas flow within the delivery unit for a preset time. This respiratory system allows for seamless switching of patients during treatment via the transfer unit, maintaining stability in gas delivery and enabling real-time monitoring of the gas status.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, and more particularly to a respiratory system for rapid switching. Background Technology

[0002] The simple respirator used clinically, also known as a balloon or breathing bag, is the simplest artificial respiration device. In situations where mechanical ventilation or other methods are unavailable, the simple respirator is an effective means of providing artificial ventilation to patients. Currently used simple respirators generally consist of a balloon, an inlet one-way valve, an outlet one-way valve, an expiratory valve, and a mask. Artificial respiration is achieved through the compression and expansion of the balloon. Although current simple respirators are simple and convenient to use, the amount of air expelled with each compression (tidal volume) cannot be precisely determined. Tidal volume control relies on the operator's experience, resulting in low accuracy. This can lead to situations where too much or too little ventilation fails to achieve the desired resuscitation effect, or even endangers the patient's life. In addition to simple respirators, there are now mechanical ventilation systems, including positive pressure and negative pressure systems, which mainly consist of a gas supply device, a control device, and a patient airway. In existing disease cases, lung collapse is a condition requiring treatment with a simple ventilator and / or mechanical ventilation. Lung collapse refers to the state where previously air-filled lung tissue collapses and closes due to air loss. Lung collapse is acquired, more common in adults, and has three types: ① Obstructive (absorbative) lung collapse: This occurs when the bronchi are compressed by nearby enlarged lymph nodes or tumors, or when the bronchi are blocked by tumors, foreign bodies, blood clots, etc., preventing air from entering the corresponding peripheral lung tissue. The existing air is gradually absorbed, leading to a group of lobules or even the entire lung lobe becoming airless and shrinking. ② Compressive lung collapse: This occurs when large amounts of pleural effusion, spontaneous pneumothorax, severe spinal deformities, or large abdominal tumors or large amounts of ascites elevate the diaphragm, thereby compressing the lung tissue and causing the alveoli to collapse and become airless. ③ Contractile lung collapse: This is caused by extensive fibrosis of the lung tissue, resulting in fibrosis and contraction. Lung recruitment primarily refers to the use of manual lung recruitment techniques, positive end-expiratory pressure (PEEP), and other methods to re-expand collapsed alveoli. Atelectasis is usually caused by the collapse of partial lung structures due to various reasons, leading to a reduction in lung volume and impaired gas exchange. Lung recruitment is mainly performed using protective lung ventilation modes. This typically involves intermittently applying pressure higher than the normal airway pressure during mechanical ventilation and maintaining this pressure for a period of time. This allows collapsed alveoli to re-expand and can prevent secondary atelectasis caused by low tidal volume ventilation, thus preventing pulmonary complications. The protective ventilation modes used for lung recruitment are primarily achieved using a portable respirator and / or a mechanical ventilator.

[0003] The prior art, such as the patent document with publication number CN114917438A, proposes a ventilator operating method and ventilator based on flow rate control, which relates to the field of medical device technology. It includes: triggering the start of ventilator ventilation by setting gas flow rate or time. The ventilator outputs two constant flow rates of the same or different magnitudes in the inspiratory and expiratory phases, respectively, thereby generating three ventilation types, including: forward ventilation type when the inspiratory flow rate is greater than the expiratory flow rate, constant flow ventilation type when the inspiratory flow rate is equal to the expiratory flow rate, and reverse ventilation type when the inspiratory flow rate is less than the expiratory flow rate.

[0004] While the existing technology described above can regulate the constant flow rate of gas during the expiratory and inspiratory phases through flow rate control, it still overlooks certain specific issues. For example, ventilators may need to be disconnected mid-use for specific reasons, such as intensive care unit ventilators configured to provide prolonged mechanical respiratory support, and operating room ventilators configured to provide anesthetic gases and respiratory support while the patient is under general anesthesia. During treatment, patients receiving respiratory support may need to be transferred between ventilator systems. An example of such a transfer may occur when a patient switches from respiratory support on an anesthesia ventilator used during surgery to respiratory support on an intensive care unit ventilator that may be connected before and / or after surgery. This transfer necessarily requires disconnecting the patient from the current ventilator before connecting to another ventilator, creating a time interval between disconnection and receiving respiratory support from either ventilator. This connection and disconnection also exposes the patient's airway to pathogens and may lead to nosocomial infections.

[0005] Furthermore, on the one hand, there are differences in understanding among those skilled in the art; on the other hand, the inventors studied a large number of documents and patents when making this invention, but due to space limitations, not all details and contents were listed in detail. However, this does not mean that the present invention does not possess the features of these prior art. On the contrary, the present invention already possesses all the features of the prior art, and the applicant reserves the right to add relevant prior art to the background art. Summary of the Invention

[0006] To address the problems of intermittent breathing and airway exposure during switching between existing ventilators, as well as the issues raised by the prior art, this application proposes a rapid switching respiratory system. The system includes a delivery unit for supplying gas to the patient; a monitoring unit for monitoring gas flow rate and tidal volume; and a transfer unit for connecting the delivery unit to different gas sources. The monitoring unit monitors the gas flow information directly received by the patient within the buffer chamber, installed between the buffer chamber and the regulating chamber of the delivery unit. A control unit within the delivery unit adjusts the delivery unit based on the flow information acquired by the monitoring unit. The transfer unit connects the delivery unit to different gas sources by opening different connection channels according to preset rules, ensuring a stable gas flow within the delivery unit for a preset time.

[0007] When using respiratory support devices for lung recruitment therapy in cases of lung collapse, strict requirements are placed on the pressure, flow rate, and continuity of the ventilation gases. Providing continuous respiratory support to patients presents several challenges, especially when intubated patients must be transferred between ventilators. One major issue is the continuous maintenance of positive end-expiratory pressure, and another is infection prevention as described above. Furthermore, the inventors have recognized that optimal patient monitoring can be provided when a consistent and continuous ventilation connection is maintained, including a constant connection from the patient connection device to the ventilator and the use of consistent ventilation parameters without interrupting continuity. Through the specific solution of this application, the monitoring unit can monitor the state of the gas in the delivery unit in real time, such as gas flow rate, tidal volume, oxygen content, and positive end-expiratory pressure. The control unit dynamically adjusts the gas state based on the above information to ensure that the patient avoids complications caused by changes in gas state during treatment. Secondly, the control unit can also adjust the transfer unit based on the information obtained by the monitoring unit. The transfer unit can switch seamlessly between different gas sources (from ventilator to portable respirator or from portable respirator to ventilator) based on the control signal of the control unit, thereby ensuring that the gas state in the delivery unit does not fluctuate due to changes in gas source, so that the patient can obtain the best treatment effect during treatment.

[0008] Preferably, the regulating chamber refreshes the gas in the buffer chamber by configuring several inlet one-way valves and several outlet one-way valves that can adjust the gas flow direction. The regulating chamber is also configured with a positive end-expiratory pressure valve for humidifying the gas and an air-oxygen mixing unit for adjusting the oxygen concentration. Specifically, only one of the inlet and outlet one-way valves is always open. When the patient inhales, the inlet one-way valve is open and the outlet one-way valve is closed, so that fresh gas introduced through the inlet one-way valve flows from the exchange chamber into the buffer chamber and is inhaled by the patient. When the patient exhales, the inlet one-way valve is closed and the outlet one-way valve is open, so that the exhaled gas flows from the buffer chamber into the exchange chamber and is discharged through the outlet one-way valve, thereby completing the gas refresh in the buffer chamber. Its advantages lie in the fact that the gas flow rate can be controlled by the valve to regulate the tidal volume, the positive end-expiratory pressure valve can control the positive end-expiratory pressure of the gas, and the oxygen concentration can be controlled by the air-oxygen mixing unit. The buffer chamber is in direct contact with the patient's face, and the above-mentioned devices are set in the regulating chamber connected to the buffer chamber, which reduces the transmission distance between the gas state regulating device and the patient, and ensures that the gas inhaled by the patient is in the most suitable state while effectively regulating the gas state.

[0009] Preferably, the flow information acquired by the monitoring unit includes at least the gas flow rate. The control unit adjusts the airflow of several inlet and outlet one-way valves based on the flow rate to ensure that the flow rate is in a suitable state. Its advantage is that the monitoring unit can monitor the gas flow rate in real time and provide real-time feedback to the control unit. The control unit adjusts the valve size based on the real-time trend of the flow rate change, thereby ensuring that the flow rate is always dynamically maintained within a preset range.

[0010] Preferably, the flow information acquired by the monitoring unit includes at least the oxygen content ratio of the gas. The control unit adjusts the ventilation rate of the pure oxygen inlet valve based on the oxygen content ratio and uses the air-oxygen mixing unit to adjust the oxygen content ratio of the gas to ensure that the oxygen content ratio is in a suitable state. Its advantage is that the monitoring unit can monitor the oxygen content ratio of the gas in real time and provide real-time feedback to the control unit. The control unit adjusts the size of the one-way valve at the pure oxygen inlet based on the real-time trend of the oxygen content ratio, thereby ensuring that the oxygen content ratio is always dynamically maintained within a preset range.

[0011] Preferably, the flow information acquired by the monitoring unit includes at least the positive end-expiratory pressure (PEEP) of the gas. The control unit adjusts the PEEP valve based on the PEEP to ensure that the airway pressure in the patient's airway is greater than the pressure in the buffer chamber at the end of expiration. Similarly, the monitoring unit can monitor the PEEP in real time and provide real-time feedback to the control unit. The control unit adjusts the PEEP valve based on the real-time trend of PEEP changes to ensure that the PEEP is always dynamically maintained within a preset range.

[0012] Preferably, the adapter connects the delivery unit to different external gas sources in a manner that is disposed at the distal end of the delivery unit, wherein the proximal end of the delivery unit is the end of the delivery unit that is in direct contact with the patient, and the distal end of the delivery unit is the end of the delivery unit that is connected to the gas source.

[0013] Preferably, the adapter has at least three openings, wherein the adapter includes a third opening connected to the main channel of the delivery unit, the adapter also includes at least a first opening connected to a first branch of the simple respirator, and the adapter also includes at least a second opening connected to a second branch of the ventilator, wherein at least one of the first branch and the second branch is in communication with the main channel.

[0014] Preferably, a circular turntable is provided at the end of the main channel that connects to the first branch and / or the second branch, and a through hole with the same diameter as the first branch and the second branch is opened at a position off-center of the circular turntable.

[0015] Preferably, the first branch and the second branch are located at different positions on the path that the through hole on the circular turntable passes through when the circular turntable rotates.

[0016] Preferably, the control unit compares the gas flow rate obtained by the monitoring unit with a preset gas flow rate. When the obtained flow rate is lower than the preset flow rate, the control unit drives the circular turntable to rotate, causing the through hole to move from one branch to another. Attached Figure Description

[0017] Figure 1 This is a simplified overall structural diagram of the respiratory system of the present invention;

[0018] Figure 2 This is a simplified cross-sectional structural diagram of the adapter of the present invention.

[0019] List of reference numerals

[0020] 100: Conveying section; 200: Monitoring section; 300: Transfer section; 101: Inlet one-way valve; 102: Outlet one-way valve; 103: Adjustment chamber; 104: Buffer chamber; 105: Air-oxygen mixing unit; 106: Positive end-expiratory pressure valve; 107: Pure oxygen inlet; 108: Exchange chamber; 301: Main channel; 302: First branch; 303: Second branch; 304: Circular turntable; 305: Groove; 306: Through hole. Detailed Implementation

[0021] The present invention will now be described in detail with reference to the accompanying drawings.

[0022] Example 1

[0023] Figure 1 This application discloses a respiratory system for rapid switching, comprising a delivery unit 100 for providing gas to a patient; a monitoring unit 200 for monitoring gas flow rate and tidal volume; and a transfer unit 300 for connecting the delivery unit 100 to different gas sources. The monitoring unit 200 monitors the gas flow information within the buffer chamber 104, which is directly accessible to the patient, by means of a buffer chamber 104 and an adjustment chamber 103 installed in the delivery unit 100. A control unit arranged within the delivery unit 100 adjusts the delivery unit 100 based on the flow information acquired by the monitoring unit 200. The transfer unit 300 connects the delivery unit 100 to different gas sources by opening different connection channels according to preset rules, thereby maintaining a stable gas flow within the delivery unit 100 for a preset time.

[0024] When using respiratory support devices for lung recruitment therapy in cases of lung collapse, strict requirements are placed on the pressure, flow rate, and continuity of the ventilation gases. Providing continuous respiratory support to patients presents several challenges, especially when intubated patients must be transferred between ventilators. One major issue is the continuous maintenance of positive end-expiratory pressure, and another is infection prevention, as mentioned above. Furthermore, the inventors have recognized that optimal patient monitoring can be provided when a consistent and continuous ventilation connection is maintained, including a constant connection from the patient connection device to the ventilator and the use of consistent ventilation parameters without interrupting continuity. Through the specific solution of this application, the monitoring unit 200 can monitor the state of the gas in the delivery unit 100 in real time, such as the gas flow rate, tidal volume, oxygen content, and positive end-expiratory pressure (PEEP). The control unit dynamically adjusts the gas state based on the above information to ensure that the patient avoids complications caused by changes in the gas state during treatment. Secondly, the control unit can also adjust the transfer unit 300 based on the information obtained by the monitoring unit 200. The transfer unit 300 can switch seamlessly between different gas sources (from ventilator to portable respirator or from portable respirator to ventilator) based on the control signal of the control unit, thereby ensuring that the gas state in the delivery unit 100 does not fluctuate due to changes in the gas source, so that the patient can obtain the best treatment effect during treatment.

[0025] Maintaining positive end-expiratory pressure (PEEP) is a crucial aspect of continuous mechanical ventilation, especially when patients are receiving lung volume recruitment therapy. Certain medical conditions, such as lung collapse, can cause collapsed alveoli. Collapsed alveoli can lead to significant lung volume loss and impair the efficiency of gas exchange. Normally, gas exchange removes carbon dioxide from a patient's blood while introducing oxygen. Specialized forms of respiratory support, known as recruitment steps, have been developed to gradually open or "re-expand" collapsed alveoli. Re-expansion steps may use specialized medical gases (such as helium) to reduce airway resistance, in addition to other medical gases such as oxygen, nitrogen, and air, or other additives (such as surfactants). Nevertheless, recruitment steps typically involve a prescribed series of ventilation pressures, including but not limited to inspiratory and expiratory pressures. Positive end-expiratory pressure is a common component of a prescribed recruitment step. At the end of the expiratory phase of the respiratory cycle, positive end-expiratory pressure applies positive pressure to the patient's airway to "keep open" the opened alveoli, which would normally collapse under ambient pressure. Therefore, positive end-expiratory pressure therapy maintains re-expanded lung volume and preserves the lung volume gain achieved through the re-expansion step.

[0026] Re-expansion steps are typically performed over a prescribed period of time, which can be hours or days. Re-expansion steps must be performed over a period because patients requiring lung re-expansion often also have low lung strain and expect increased re-expansion volume from alveolar opening rather than lung expansion. Therefore, as more alveoli re-expand and lung volume increases, the pressure applied to the lungs slowly increases over time with each re-expansion step. However, as mentioned above, when a patient is transferred between ventilators at some point in the transition, the patient must typically be disconnected from one ventilator and reconnected to another. Even if this transition period is short, the loss of positive end-expiratory pressure maintained in the system can cause the re-expanded alveoli to collapse, resulting in the loss of any physiological gains already achieved through previous re-expansion steps and other respiratory support. One or more new re-expansion steps must be performed over the aforementioned hours or days to re-expand the lost lung volume.

[0027] To address the aforementioned issues, the present invention designs a transfer unit 300 capable of quickly switching between different gas sources. The transfer unit 300 is positioned at the distal end of the delivery unit 100 to connect the delivery unit 100 to different external gas sources. The proximal end of the delivery unit 100 is the end that directly contacts the patient, and the distal end of the delivery unit 100 is the end that connects to the gas source.

[0028] Preferably, the adapter 300 connects the conveying unit 100 to different gas sources by opening different connection channels according to preset rules, so that the gas flow inside the conveying unit 100 remains stable within a preset time. The preset rules include at least the following: the adapter 300 can automatically switch interfaces based on the gas flow information monitored by the monitoring unit 200 from the processing unit; the adapter 300 can also switch interfaces based on commands manually applied to the processing unit; and the adapter 300 can automatically switch interfaces at a preset frequency according to a preset time.

[0029] Preferably, the adapter 300 has at least three openings, including a third opening that connects to the main channel 301 of the delivery unit 100, a first opening that connects to the first branch 302 of the simple respirator, and a second opening that connects to the second branch 303 of the ventilator. At least one of the first branch 302 and the second branch 303 is in communication with the main channel 301.

[0030] Specifically, the adapter 300 is equipped with a housing including a main channel 301, a first branch 302 and a second branch 303. At least inside the housing, the positions of the first branch 302 and the second branch 303 are defined by the housing, that is, inside the housing, the positions of the first branch 302 and the second branch 303 are fixed relative to the housing.

[0031] Preferably, a circular turntable 304 is provided at the end of the main channel 301 that connects to the first branch 302 and / or the second branch 303. The circular turntable 304 has a through hole 306 at a position off-center, which is the same size as the opening of the first branch 302 and the second branch 303.

[0032] Specifically, with the circular turntable 304 as the dividing line, the first branch 302 and the second branch 303 belong to the two ends of the main channel 301. However, the extension direction of the first branch 302, the second branch 303 and the main channel 301 near the circular turntable 304 is orthogonal to the circular turntable 304. In essence, the circular turntable 304 is a multi-way distribution flange set inside the housing, connecting the main channel 301 with the first branch 302 and / or the second branch 303. More specifically, the ends of the main channel 301, the first branch 302 and the second branch 303 near the circular turntable 304 are provided with a certain distance of rigid passage. At the end of the rigid passage, an annular sealing ring of a corresponding size is provided. When the circular turntable 304 rotates, the annular sealing ring will undergo relative displacement with the disk surface of the circular turntable 304. Specifically, the circular turntable 304 is embedded in the housing, or the circular turntable 304 is connected to the housing via sliding balls, ensuring that the axis of the circular turntable 304 is in the same straight line as the axis of the housing. In this way, the circular turntable 304 can rotate around the axis of the housing inside the housing of the connecting part 300. The device that drives the circular turntable 304 to rotate can be configured inside the housing. The main channel 301 is on the side opposite to the circular turntable 304. Specifically, the driving device is fixedly connected to the circular turntable 304 via a shaft. The driving device is at least sandwiched in the middle by the first branch 302 and the second branch 303. There is at least a certain gap between the driving device and the shaft and the first branch 302 and the second branch 303 to avoid friction between the shaft and the outer wall of the first branch 302 and the second branch 303 when the driving device drives the circular turntable 304 to rotate.

[0033] according to Figure 2As shown, the first branch 302 and the second branch 303 are located at different positions on the path traversed by the through hole 306 on the circular turntable 304 as the circular turntable 304 rotates. Specifically, the size of the through hole 306 on the circular turntable 304 is the same as the size of the first branch 302 and the second branch 303. When the circular turntable 304 rotates to a specific position, the center of the through hole 306 on the circular turntable 304 is at least a certain distance from the center of the circular turntable 304. This center-to-center distance is at least greater than the sum of the radius of the first branch 302 or the second branch 303 and the radius of the driving device, thereby ensuring that when the first branch 302 and / or the second branch 303 are aligned with the through hole 306, they will not collide with each other or with the driving device and the shaft connecting the driving device. Furthermore, an annular groove 305 is formed on the circular turntable 304. Specifically, the groove 305 is the trajectory of the through hole 306 at an eccentric position on the circular turntable 304 when the circular turntable 304 rotates around the housing or the axis of the circular turntable 304. The annular width of the groove 305 is the same as the diameter of the through hole 306. The annular sealing rings of the first branch 302 and the second branch 303 are precisely embedded inside the groove 305. Specifically, the surface of the groove 305 is also coated with a sealing layer. When the first branch 302 and the second branch 303 can move within the groove 305, the annular sealing rings of the first branch 302 and the second branch 303 still closely abut against the sealing layer in the groove 305, providing a good sealing effect for the passage formed by the first branch 302 and / or the second branch 303 and the through hole 306. Specifically, an automatic valve is installed inside the through hole 306, which can adjust the opening and closing state of the through hole 306 under the control of the control unit. Before the drive device drives the circular turntable 304 to rotate, the control unit controls the automatic valve to close the through hole 306, thereby ensuring that the main channel 301 connected by the through hole 306 remains closed to the outside world during the rotation of the circular turntable 304, and preventing the main channel 301 from being contaminated by the external environment during the rotation.

[0034] Preferably, the branch connected to the circular turntable 304 of this application can be configured as needed to provide a third branch, a fourth branch, etc., for conveying additional gas sources.

[0035] Preferably, the control unit compares the gas flow rate obtained by the monitoring unit 200 with the preset gas flow rate. When the obtained flow rate is lower than the preset flow rate, the control unit drives the circular turntable 304 to rotate, causing the through hole 306 to move from the position of one branch to the position of another branch.

[0036] The adapter 300 of this application also has another configuration. (See reference...) Figure 2In this configuration, the first branch 302 and the second branch 303 are closely fitted together on the circular turntable 304. Specifically, the openings of the first branch 302 and the second branch 303 are designed as fan-shaped structures that conform to the annular shape of the groove 305.

[0037] Preferably, according to the above method, the shape of the through hole 306 on the circular turntable 304 is correspondingly designed to maintain the same shape as the first opening of the first branch 302 and the second opening of the second branch 303. The first opening and the second opening are arranged in a manner close to each other's sidewalls inside the annular groove 305 of the circular turntable 304. In this manner, the rotation angle of the circular turntable 304 is further reduced. The specific rotation angle is related to the size of the first opening and the second opening, and the rotation angle of the circular turntable 304 can be determined according to the central angle formed by the two edges of the first opening and the second opening.

[0038] Preferably, during the rotation of the circular turntable 304, the connection state between the through hole 306 and the first and second openings dynamically changes. For example, in a certain state, the through hole 306 completely overlaps with the first opening, the first branch 302 is connected to the main channel 301, the second opening is blocked by the portion of the groove 305 that does not cover the through hole 306, and the second branch 303 is disconnected from the main channel 301. When it is necessary to adjust the branch connected to the main channel 301 through the circular turntable 304, rotating the circular turntable 304 causes the through hole 306 to move from the first opening to the second opening. During this movement, the area of ​​the part of the through hole 306 connected to the first opening gradually decreases, while at the same time the area of ​​the part of the through hole 306 connected to the second opening gradually increases until the second opening completely overlaps with the through hole 306, and the first opening is completely blocked.

[0039] In this method, the through hole 306 no longer needs to be equipped with an automatic valve to block the through hole 306. In this method, the through hole 306 is always in the connection passage of the first branch 302 and / or the second branch 303. Compared with the arrangement of the aforementioned adapter 300, this method has a smaller rotation range and requires less rotation time, which meets the requirements of this system.

[0040] Example 2

[0041] For simple respirators, the existing working principle is as follows: Oxygen enters through the positive pressure inlet valve, and as the balloon deflates, the negative pressure inlet valve opens, temporarily storing the oxygen inside the balloon. If the oxygen flow is insufficient, the negative pressure opens the negative pressure inlet valve, allowing air to fill the respirator. Excess oxygen after the balloon deflates is stored in the oxygen bag. If the oxygen flow is excessive, the positive pressure outlet valve opens, expelling excess gas from the respirator. When the balloon is squeezed, positive pressure is generated, forcibly pushing the airflow inlet valve open and blocking the negative pressure outlet valve. The gas inside the balloon is then delivered to the patient through the central incision of the airflow inlet valve. When the balloon is released, the airflow inlet valve immediately pushes upward and closes, allowing the patient's exhaled gas to be released through the outlet airflow valve. Meanwhile, the negative pressure inlet check valve opens due to the negative pressure generated by the release of the balloon, allowing oxygen from the reservoir bag to enter the balloon until it fully recovers. This cycle is then repeated by squeezing the balloon again. The safety valve is designed to prevent barotrauma caused by excessive airway pressure when the balloon is squeezed. Specifically, if the airway pressure is set to 60 cmH2O, the safety valve opens when the pressure exceeds this limit, expelling gas from the respiratory tract without forcibly forcing it into the lungs. However, this device simply introduces gas into the patient's body; it cannot precisely control gas states such as tidal volume, gas rate, and oxygen content. Therefore, in the transition between ventilators, simply using a simplified respirator as a substitute for a ventilator may result in gas states that do not meet the patient's treatment needs. Therefore, this application proposes an implementation scheme that allows for monitoring and regulation of the gas state even after switching. Specifically, this application proposes a respiratory system for rapid switching, including a delivery unit 100 for supplying gas to a patient; a monitoring unit 200 for monitoring the gas flow rate and tidal volume; and a transfer unit 300 for transferring the delivery unit 100 to different gas sources. The monitoring unit 200 monitors the gas flow information within the buffer chamber 104, which is directly accessible to the patient, by being installed between the buffer chamber 104 and the regulating chamber 103 of the delivery unit 100. A control unit arranged within the delivery unit 100 regulates the delivery unit 100 based on the flow information acquired by the monitoring unit 200. The transfer unit 300 connects the delivery unit 100 to different gas sources by opening different connection channels according to preset rules, ensuring that the gas flow within the delivery unit 100 remains stable for a preset time. Specifically, the stable flow state means that when the gas exchanges and flows within the transmission section 100, its flow rate, oxygen concentration, gas pressure, and other parameters will not change abruptly at any given moment, or its flow rate, oxygen concentration, and gas pressure will be within a normal, conventional preset range. For example, the inspiratory flow rate is generally adjusted to 40-100 L / min based on the patient's inspiratory strength and minute ventilation.Since the inspiratory flow rate directly affects the patient's spontaneous breathing, the inspiratory flow rate should be less than 40 L / min.

[0042] Preferably, the transfer unit 300 can transfer the gas source based on the specific information detected by the monitoring unit 200. Specifically, when the monitoring unit 200 detects that the tidal volume or gas flow rate of the gas is lower than a preset range, the processing unit will drive the transfer unit 300 to transfer the interface from the original interface to another interface and issue a relevant transfer signal, which may be an alarm message such as light or sound.

[0043] Preferably, the regulating chamber 103 refreshes the gas in the buffer chamber 104 by configuring a plurality of inlet one-way valves 101 and a plurality of outlet one-way valves 102. The regulating chamber 103 is also configured with an end-expiratory positive pressure valve 106 that can adjust the positive end-expiratory pressure and an air-oxygen mixing unit 105 that can adjust the oxygen concentration. Its advantage is that the gas flow rate can be controlled by the valves, the end-expiratory positive pressure of the gas can be controlled by the end-expiratory positive pressure valve 106, and the oxygen concentration can be controlled by the air-oxygen mixing unit 105. The buffer chamber 104 is in direct contact with the patient's face, and the above-mentioned devices are set in the regulating chamber 103 connected to the buffer chamber 104, which reduces the transmission distance between the gas state regulating device and the patient, and ensures that the gas inhaled by the patient is in the most suitable state while effectively regulating the gas state.

[0044] Preferably, the flow information acquired by the monitoring unit 200 includes at least the gas flow rate. The control unit adjusts the airflow of several inlet one-way valves 101 and outlet one-way valves 102 based on the flow rate to ensure that the flow rate is adapted. Its advantage is that the monitoring unit 200 can monitor the gas flow rate in real time and provide real-time feedback to the control unit. The control unit adjusts the valve size based on the real-time trend of the flow rate change, thereby ensuring that the flow rate is always dynamically maintained within a preset range.

[0045] Specifically, the control unit can adjust the orifice diameter of the inlet one-way valve 101 and the outlet one-way valve 102. Furthermore, by controlling the opening and closing states of the inlet one-way valve 101 and the outlet one-way valve 102 at a specific frequency, the delivery unit 100 can be adjusted to adapt to the patient's inhalation and respiration rates.

[0046] Preferably, the monitoring unit 200 can also detect the gas pressure inside the conveying unit 100 through a pressure sensor installed in the conveying unit 100. The monitoring unit 200 obtains the gas flow rate and flow direction through a flow rate sensor. The control unit can adjust the internal pressure through the pressure module of the conveying unit 100, thereby adjusting the gas flow rate in conjunction with the orifice size of the valve.

[0047] Regarding the rates of inspiration and expiration, when using the respiratory system of this application for assisted ventilation, if spontaneous breathing is present, the ideal inspiratory flow rate should precisely meet the patient's peak inspiratory flow requirement. The inspiratory flow rate is generally adjusted to 40–100 L / min based on the patient's inspiratory force and minute ventilation. Since the inspiratory flow rate directly affects the patient's spontaneous breathing, it should be below 40 L / min. When using pressure-controlled ventilation with this system, the peak inspiratory flow rate is determined by both the preset pressure level and the patient's inspiratory force; the maximum inspiratory flow rate is limited by the ventilator's performance. The ratio of inspiration to expiration should take into account factors such as the impact of mechanical ventilation on the patient's hemodynamics, oxygenation status, and level of spontaneous breathing. For patients with spontaneous breathing, when using a ventilator for assisted breathing, the ventilator's delivery of air should be coordinated with the patient's inhalation to ensure synchronization. Generally, inhalation takes 0.8 to 1.2 seconds, and the inspiratory-to-expiratory ratio is 1:2 to 1:1.5. For patients under controlled ventilation, the inspiratory time is generally longer and the inspiratory-to-expiratory ratio is higher, which can increase the mean airway pressure and improve oxygenation.

[0048] Preferably, adjusting the flow rates of the expiratory and inspiratory phases of the gas allows for further control of the tidal volume of the respiratory system described in this application. Tidal volume (TV) refers to the volume of air inhaled or exhaled during each quiet breath. It is related to age, sex, body volume, breathing habits, and metabolism. The set tidal volume usually refers to the inhaled volume. The tidal volume setting is not constant and should be adjusted based on the patient's blood gas analysis.

[0049] Specifically, when using the respiratory system described in this application for assisted ventilation, the goal of tidal volume setting is to ensure adequate ventilation and patient comfort. The typical tidal volume for adults is 5–15 m³ / kg, with 8–12 m³ / kg being the most commonly used range. The following factors should be considered when setting the tidal volume: lung compliance, airway resistance, compressible volume of the ventilator tubing, oxygenation function, and the risk of barotrauma. Barotrauma and other ventilator-related injuries are caused by improper use of mechanical ventilation. To prevent barotrauma during tidal volume setting, the airway plateau pressure should generally not exceed 35–40 cmH2O. For pressure-controlled ventilation, the tidal volume is primarily determined by the preset pressure level, the patient's inspiratory strength, and airway resistance.

[0050] Preferably, the flow information acquired by the monitoring unit 200 includes at least the oxygen content ratio of the gas. The control unit adjusts the ventilation rate of the one-way valve of the pure oxygen inlet 107 based on the oxygen content ratio and uses the air-oxygen mixing unit 105 to adjust the oxygen content ratio of the gas to ensure that the oxygen content ratio is in a suitable state. Its advantage is that the monitoring unit 200 can monitor the oxygen content ratio of the gas in real time and provide real-time feedback to the control unit. The control unit adjusts the size of the one-way valve of the pure oxygen inlet 107 based on the real-time trend of the oxygen content ratio, thereby ensuring that the oxygen content ratio is always dynamically maintained within a preset range.

[0051] Specifically, the oxygen content of the inhaled gas generally depends on the target level of arterial oxygen partial pressure, the level of positive end-expiratory pressure, mean airway pressure, and the patient's hemodynamic status. Because inhaling high concentrations of oxygen can cause oxygen toxicity-induced lung injury, the inhaled oxygen concentration is generally required to be below 50%–60%. However, in selecting the inhaled oxygen concentration, not only should the lung-damaging effects of high oxygen concentrations be considered, but also the damaging effects of excessively high airway and alveolar pressures on the lungs. For patients with severe oxygenation impairment, the inhaled oxygen concentration should be set to achieve an arterial oxygen saturation greater than 88%–90%, provided that adequate sedation and muscle relaxation are maintained and an appropriate level of positive end-expiratory pressure is used.

[0052] Preferably, the flow information acquired by the monitoring unit 200 includes at least the positive end-expiratory pressure (PEEP). The control unit adjusts the PEEP valve 106 based on the PEEP to ensure that the air pressure in the patient's airway is greater than the air pressure in the buffer chamber at the end of expiration. Similarly, the monitoring unit 200 can monitor the PEEP in real time and provide real-time feedback to the control unit. The control unit adjusts the PEEP valve 106 based on the real-time trend of PEEP changes to ensure that the PEEP is always dynamically maintained within a preset range.

[0053] In lung recruitment therapy, the main purpose of positive end-expiratory pressure (PEEP) is to increase lung volume, raise mean airway pressure, and improve oxygenation. PEEP can counteract intrinsic PEEP, reducing the inspiratory trigger work caused by intrinsic PEEP. PEEP can increase intrathoracic pressure, leading to reduced venous return and decreased left ventricular preload. For ARDS patients, the selection of PEEP levels should be based on a comprehensive consideration of factors such as inspiratory oxygen concentration, inspiratory time, arterial oxygen partial pressure level and target level, and oxygen delivery level. The development of pulmonary mechanics monitoring (pressure-volume loop) provides a basis for PEEP selection. Generally, in the early stages of acute lung injury, the PEEP level should be slightly higher than the pressure level at the lower inflection point of the lung pressure-volume loop. For patients undergoing thoracic or upper abdominal surgery, using a PEEP of 3–5 cmH2O during postoperative mechanical ventilation helps prevent postoperative atelectasis and hypoxemia.

[0054] Example 3

[0055] This embodiment is an improvement and supplement to the content of Embodiments 1 and 2, and repeated content will not be repeated.

[0056] The respiratory system of this application also includes at least a temporary ventilator connected to the first branch 302 of the adapter 300 and a monitor capable of monitoring at least one or more hemodynamic parameters of the patient and transmitting the monitored parameter information to the control unit.

[0057] Preferably, the first branch 302 of the transfer unit 300 is connected to the temporary ventilator of the system. The temporary ventilator can simulate the ventilation technique implemented by the ventilator connected to the second branch 303 for lung recruitment during the process of the transfer unit 300 gradually transferring the main channel 301 from the ventilator connected to the second branch 303 to the temporary ventilator connected to the first branch 302, based on the adjustment of the control unit, so as to complete the transfer without causing changes in the gas state in the main channel 301.

[0058] Preferably, the control unit can control the automatic compression of the temporary respirator, adjust the tidal volume of the temporary respirator by controlling the degree of compression, and adjust the ventilation frequency of the temporary respirator by controlling the compression frequency.

[0059] Preferably, the temporary respirator includes at least an air bladder and a compressor for compressing the air bladder. The compressor is mounted on a square frame that covers most of the air bladder. At least two opposing surfaces of the frame are provided with a first pressure plate and a second pressure plate that can move close to each other to compress the air bladder. The first and second pressure plates move at the same speed and maintain the same posture during movement; in other words, they remain parallel to each other, thus ensuring consistent compression of the air bladder. The first and second pressure plates are moved by screws located on the frame at edges perpendicular to the planes of the first and second pressure plates, and by a motor that drives the screws. Specifically, four screws are provided, each located at one of the aforementioned edges. The four screws pass through the four corners of the first and second pressure plates. The inner walls of the holes through which the first and second pressure plates pass through the screws are provided with threads in opposite directions, so that when the same screw rotates, the first and second pressure plates always move in opposite directions. The temporary ventilator also includes a motor control system for controlling the motor that drives the screw rotation, a data processor for parameter information of the corresponding control unit, a safety relief valve located on the outlet tube of the air bag, and a connection port connected to the first branch 302 of the adapter 300. The temporary ventilator can be detachably installed at the patient's head of the bed for easy movement with the patient.

[0060] Preferably, the control unit adjusts the parameters of the ventilator connected to the second branch 303 based on one or more of the hemodynamic parameters obtained by the monitor, or medical staff manually configure the respiratory parameters of the ventilator through the control unit and the patient's hemodynamic parameters obtained by the monitor, so that the ventilator can meet the manual requirements of lung recruitment.

[0061] Preferably, the hemodynamic parameters that the monitor can acquire include at least: oxygen saturation (SpO2), cardiac output (CO), mean arterial pressure (MAP), systolic blood pressure (SBP), and heart rate (HR). The control unit can display one or more of the hemodynamic parameters acquired by the monitor as short-trend waveforms.

[0062] Preferably, the control unit configures the specific parameters of the ventilator during lung recruitment through automatic learning or manual configuration. The parameters of the ventilator include at least: positive end-expiratory pressure, inspiratory pressure, respiratory rate, respiratory ratio, and oxygenation ratio.

[0063] Preferably, the parameters of the ventilator can be dynamically adjusted in real time based on the hemodynamic parameters obtained from the monitor.

[0064] Preferably, the control unit can be integrated into a portable smart device, such as a mobile phone or tablet; the control unit can also be integrated into a specific electronic instrument; or the control unit can be integrated into a computer device such as a computer.

[0065] For patients requiring lung recruitment, emergency and resuscitation situations are often necessary. During emergency room resuscitation, mechanical ventilation is used to assist breathing. This involves intermittently administering pressure or volume higher than the normal mean airway pressure for a certain period to re-expand collapsed alveoli. However, even after the life-threatening situation has been alleviated, patients with alveolar collapse still require continuous ventilation at specific parameters for a period after resuscitation. The contradiction lies in the fact that emergency rooms, being urgent, strained, and scarce medical resources, are not open to patients whose lives have been saved. Therefore, patient transfer is necessary. However, during transfer, the ventilator used for mechanical ventilation is disconnected. Blindly disconnecting the ventilator could potentially cause secondary life-threatening situations. Therefore, during transfer, a portable expiratory respirator is used to provide continuous mechanical ventilation. However, the problem with this method is that there is a ventilation interruption interval during the transition from mechanical ventilation to a simple respirator. The duration of this interval is closely related to the proficiency of the medical staff, and even if the staff is proficient, the time interval may still lead to the risk of secondary alveolar collapse in the patient. In addition, the mechanical ventilation parameters change from controllable to uncontrollable when transferring from a ventilator with detailed parameters to a simple respirator, and the change in mechanical ventilation parameters can easily affect the lung re-expansion process.

[0066] Therefore, the transfer unit 300 connects the delivery unit 100 to different gas sources by opening different connection channels according to the above-mentioned preset rules, so that the gas flow inside the delivery unit 100 remains stable within a preset time. The respiratory system of this application can solve the defects of unstable continuous ventilation and intermittent ventilation when transfer is required.

[0067] Preferably, the first branch 302 of the transfer unit 300 is connected to the temporary ventilator of the system. The temporary ventilator can simulate the ventilation technique implemented by the ventilator connected to the second branch 303 for lung recruitment during the process of the transfer unit 300 gradually transferring the main channel 301 from the ventilator connected to the second branch 303 to the temporary ventilator connected to the first branch 302, based on the adjustment of the control unit, so as to complete the transfer without causing changes in the gas state in the main channel 301.

[0068] Furthermore, in conjunction with the structural design of the adapter 300 of this application, when the parameters of the temporary respirator connected to the first branch 302 and the ventilator connected to the second branch 303 are the same, the gas state in the main channel 301 connected to the adapter 300 will not change during the process of the through hole 306 on the circular turntable of the adapter 300 gradually moving from the opening of the second branch 303 to the opening of the first branch 302.

[0069] Preferably, during the rotation of the circular turntable, the connection state between the through hole 306 and the first and second openings changes dynamically. For example, in a certain state, the through hole 306 completely overlaps with the first opening, the first branch 302 is connected to the main channel 301, the second opening is blocked by the portion of the groove that does not cover the through hole 306, and the second branch 303 is disconnected from the main channel 301. When it is necessary to adjust the branch connected to the main channel 301 by means of the circular turntable, rotating the circular turntable causes the through hole 306 to move from the first opening to the second opening. During this movement, the area of ​​the part of the through hole 306 connected to the first opening gradually decreases, while at the same time the area of ​​the part of the through hole 306 connected to the second opening gradually increases, until the second opening completely overlaps with the through hole 306, and the first opening is completely blocked.

[0070] Therefore, the temporary respirator can be based on the control signals and parameter information of the control unit. Before the control unit drives the circular turntable to rotate, the data processing unit of the temporary respirator receives the control information and parameter information of the control unit and sets the rotation degree and rotation interval of the drive motor based on the parameter information. The rotation degree corresponds to the compression degree of the temporary respirator, which in turn corresponds to the ventilation volume of the temporary respirator. The rotation interval corresponds to the compression interval of the temporary respirator, which in turn corresponds to the ventilation frequency of the temporary respirator.

[0071] Therefore, the temporary ventilator can accurately simulate the ventilation gas state of the ventilator, ensuring that the patient's mechanical ventilation state remains roughly the same before and after the transfer, avoiding unstable ventilation state and disruption of ventilation continuity during the transfer process, and greatly reducing the risk to the patient during the transfer process.

[0072] Preferably, the system is arranged according to the gas source's intake direction, with the adapter 300 directly connected to the gas source. In this application, the adapter 300 includes at least a first branch 302 connected to the temporary respirator of this application and a second branch 303 for connecting to a conventional ventilator. The first branch 302 and the second branch 303 can be switched to the main channel 301 under the control of the processing unit.

[0073] Preferably, the main channel 301 of the transfer unit 300 is connected to the regulating chamber 103 of the conveying unit 100, and a pure oxygen inlet 107 is provided on the air-oxygen mixing unit 105 connected to the main channel 301 to facilitate the input of a certain amount of oxygen as needed.

[0074] Preferably, the main channel 301 of the adapter 300 is connected to the air-oxygen mixing unit 105 in the regulating cavity 103 after entering the regulating cavity 103. The air-oxygen mixing unit 105 can fully mix the gas delivered from the main channel 301.

[0075] Preferably, after the air-oxygen mixing unit 105 has fully mixed the gas, the gas is transported to the exchange chamber 108 in the regulating chamber 103, wherein the exchange chamber 108 and the pipe connected to the air-oxygen mixing unit 105 are connected by an air inlet check valve 101.

[0076] Preferably, an exhaust one-way valve 102 is installed on the surface of the exchange chamber 108 opposite to the inlet one-way valve 101. A monitoring unit 200 is provided on the side of the exchange chamber 108 where no valve is installed, at the same distance from the inlet one-way valve 101 and the exhaust one-way valve 102. After passing through the monitoring unit 200, the gas is connected to the buffer chamber through a pipeline.

[0077] Preferably, a positive end-expiratory pressure valve 106 is connected to the one-way valve 102 to regulate the positive end-expiratory pressure, ensuring that at the end of each breath, the pressure in the patient's airway is greater than the pressure in the buffer chamber and the exchange chamber.

[0078] Specifically, the monitoring unit 200 can monitor the state of the gas, including tidal volume, flow rate, oxygen content, positive end-expiratory pressure, and other information. The monitoring unit 200 transmits the monitored information to an external device of the configured processing unit via wired or wireless means. The processing unit can dynamically display the above information as an image on the display screen of the external device according to the time-varying pattern, and the processing unit adjusts the gas state of the corresponding components in real time according to the dynamic trend of the above information.

[0079] It should be noted that the specific embodiments described above are exemplary, and those skilled in the art can devise various solutions inspired by the disclosure of this invention. These solutions all fall within the scope of this invention and its protection. Those skilled in the art should understand that this specification and its accompanying drawings are illustrative and not intended to limit the scope of the claims. The scope of protection of this invention is defined by the claims and their equivalents.

Claims

1. A respiratory system for rapid switching, characterized in that, The respiratory system includes: Delivery unit (100) for providing gas to the patient; The monitoring unit (200) is used to monitor the gas flow rate and tidal volume; A transfer unit (300) is used to transfer the delivery unit (100) to different gas sources; The monitoring unit (200) monitors the gas flow information in the buffer chamber (104) directly obtained by the patient by means of being installed between the buffer chamber (104) and the regulating chamber (103) of the delivery unit (100), and the control unit arranged in the delivery unit (100) regulates the delivery unit (100) based on the flow information obtained by the monitoring unit (200); The adapter (300) connects the conveying unit (100) to different gas sources by opening different connection channels according to preset rules, so that the gas flow inside the conveying unit (100) remains stable within a preset time. The adapter (300) is equipped with a housing including a main channel (301), a first branch (302) and a second branch (303). At least inside the housing, the positions of the first branch (302) and the second branch (303) are defined by the housing. A circular turntable (304) is provided at the end of the main channel (301) that connects to the first branch (302) and / or the second branch (303). A through hole (306) with the same diameter as the first branch (302) and the second branch (303) is opened at a position off-center of the circular turntable (304). The control unit compares the gas flow rate obtained by the monitoring unit (200) with the preset gas flow rate. When the obtained flow rate is lower than the preset flow rate, the control unit drives the circular turntable (304) to rotate so that the through hole (306) moves from the position of one branch to the position of the other branch.

2. The respiratory system for rapid switching according to claim 1, characterized in that, The regulating chamber (103) refreshes the gas in the buffer chamber (104) by configuring a plurality of inlet one-way valves (101) and a plurality of outlet one-way valves (102) that can adjust the gas flow direction. The regulating chamber (103) is also configured with an end-expiratory positive pressure valve (106) that can control the end-expiratory positive pressure and an air-oxygen mixing unit (105) that can adjust the oxygen concentration.

3. The respiratory system for rapid switching according to claim 2, characterized in that, The flow information acquired by the monitoring unit (200) includes at least the gas flow rate. The control unit adjusts the ventilation volume of several inlet one-way valves (101) and outlet one-way valves (102) based on the flow rate to ensure that the flow rate is in a suitable state, and further adjusts the tidal volume.

4. The respiratory system for rapid switching according to claim 3, characterized in that, The flow information acquired by the monitoring unit (200) includes at least the oxygen content ratio of the gas. The control unit adjusts the ventilation volume of the valve of the pure oxygen inlet (107) based on the oxygen content ratio and uses the air-oxygen mixing unit (105) to adjust the oxygen content ratio of the gas to ensure that the oxygen content ratio is in a suitable state.

5. The respiratory system for rapid switching according to claim 4, characterized in that, The flow information acquired by the monitoring unit (200) includes at least the positive end-expiratory pressure of the gas. The control unit adjusts the positive end-expiratory pressure valve (106) based on the positive end-expiratory pressure to ensure that the airway pressure in the patient's body at the end of expiration is greater than the gas pressure in the buffer chamber (104).

6. The respiratory system for rapid switching according to claim 5, characterized in that, The adapter (300) is disposed at the distal end of the delivery unit (100) to connect the delivery unit (100) to different external gas sources, wherein the proximal end of the delivery unit (100) is the end of the delivery unit (100) that is in direct contact with the patient, and the distal end of the delivery unit (100) is the end of the delivery unit (100) that is connected to the gas source.

7. The respiratory system for rapid switching according to claim 6, characterized in that, The adapter (300) has at least three openings, including a third opening that connects to the main channel (301) of the delivery unit (100), the adapter (300) also includes at least a first opening that connects to the first branch of the simple respirator, and the adapter (300) also includes at least a second opening that connects to the second branch of the ventilator, wherein at least one of the first branch and the second branch is in communication with the main channel (301).

8. The respiratory system for rapid switching according to claim 7, characterized in that, The first branch and the second branch are located at different positions on the path that the through hole on the circular turntable passes through when the circular turntable rotates.

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