Respiratory ventilation method, apparatus, anaesthesia machine and computer readable storage medium

Abstract

A respiratory ventilation method, device, anesthesia machine and computer readable storage medium; the respiratory ventilation device comprises: a patient end respiratory system (1), a machine end respiratory system (2), a flow monitor (3) and a processor (4); in the inspiration stage, the first gas in the expiratory container (22) of the machine end respiratory system (2) is driven by the driving gas to the patient end respiratory system (1), transmitted to the patient interface (10) by the patient end respiratory system (1), and the first flow of the driving gas in the expiratory container (22) is detected by the flow monitor (3); in the expiration stage, the expiration gas is received from the patient interface (10), transmitted to the expiratory container (22) through the patient end respiratory system (1), the excess mixed gas in the patient end respiratory system (1) is discharged through the exhaust branch (23), and the second flow of the mixed gas is detected by the flow monitor (3); the processor (4) can calculate the tidal volume of a respiratory cycle based on the first flow and the second flow.

Description

[0001] This application is a divisional application of Chinese patent application No. 202080108300.5, entitled “Respiratory Ventilation Method, Device, Anesthesia Machine and Computer-Readable Storage Medium”, filed on December 31, 2020. Technical Field

[0002] The present invention relates to the field of medical device technology, and in particular to a breathing ventilation method, device, anesthesia machine and computer-readable storage medium. Background Technology

[0003] Currently, monitoring tidal volume during patient ventilation is a crucial function of anesthesia machines. Depending on the measurement site, existing tidal volume monitoring solutions for anesthesia machines are mainly divided into two types: patient-side monitoring and machine-side monitoring. Patient-side monitoring places the sensor very close to the patient's airway. Because the sensor is close to the airway, patient-side monitoring has advantages such as accuracy and high sensitivity. However, precisely because the sensor is close to the airway, it is easily affected by airway secretions and exhaled moisture condensation. Over time, this can lead to sensor drift or deviation, resulting in inaccurate tidal volume measurements and even ventilation control failure, ultimately causing inaccurate tidal volume detection. Summary of the Invention

[0004] The present invention provides a respiratory ventilation method, device, anesthesia machine, and computer-readable storage medium, which can improve the accuracy of tidal volume detection.

[0005] The technical solution of this invention can be implemented as follows:

[0006] This invention provides a respiratory ventilation device, including: a patient-end respiratory system, a machine-end respiratory system, a flow monitor, and a processor;

[0007] The machine-based breathing system includes: an intake branch for the inhalation phase, a breathing container, and an exhaust branch for the exhalation phase.

[0008] Both the intake branch and the exhaust branch are connected to the breathing container via the flow monitor, and the breathing container is connected to the patient-end breathing system.

[0009] The processor is connected to the flow monitor; wherein...

[0010] During the inhalation phase, driving gas is transmitted on the intake branch to drive the first gas in the breathing container to the patient-end breathing system, which then transmits it to the patient interface, and the first flow rate of the driving gas in the breathing container is detected by the flow monitor.

[0011] During the exhalation phase, expiratory gas is received from the patient interface and transmitted to the breathing container through the patient-end breathing system. Excess mixed gas in the breathing container is discharged through the exhaust branch, and the second flow rate of the mixed gas is detected by the flow monitor.

[0012] The processor is configured to calculate the tidal volume of one respiratory cycle based on the first flow rate and the second flow rate.

[0013] In the above-mentioned breathing ventilation device, the flow monitor is a bidirectional flow sensor.

[0014] In the above-mentioned breathing ventilation device, the flow monitor is a unidirectional flow sensor; the flow monitor includes: a first flow sensor and a second flow sensor;

[0015] The first flow sensor is connected to the intake branch, and the second flow sensor is connected to the exhaust branch;

[0016] During the inhalation phase, the first flow rate of the driving gas in the breathing container is detected by the first flow sensor;

[0017] During the exhalation phase, the second flow rate of the mixed gas is detected by the second flow sensor.

[0018] The above-mentioned breathing ventilation device further includes: a first one-way valve and a second one-way valve; the flow monitor is a one-way flow sensor; the flow monitor includes: a first flow sensor and a second flow sensor;

[0019] The first one-way valve is used to deliver the driving gas to the breathing container;

[0020] The second check valve is used to transfer the mixed gas to the exhaust branch;

[0021] Both the intake branch and the exhaust branch are connected to the breathing container through the first flow sensor, the first one-way valve, the second flow sensor, and the second one-way valve; the first one-way valve is connected to the first flow sensor, and the second one-way valve is connected to the second flow sensor.

[0022] During the inhalation phase, the first flow rate of the driving gas in the breathing container is detected by the first flow sensor and the first one-way valve;

[0023] During the exhalation phase, the second flow rate of the mixed gas is detected by the second flow sensor and the second one-way valve.

[0024] The above-mentioned breathing ventilation device further includes: a gas delivery branch; the gas delivery branch is equipped with a third flow sensor, a fresh gas interface and an evaporator;

[0025] During the inhalation phase, a second gas is received through the fresh gas interface, the second gas is transmitted to the evaporator, a third gas is drawn out, and the third gas is transmitted to the patient interface via the patient-end respiratory system; and the third flow rate of the third gas delivered by the gas delivery branch is detected by the third flow sensor.

[0026] During the exhalation phase, a fourth gas is received through the fresh gas interface, the fourth gas is transmitted to the vaporizer, a fifth gas is carried out, and the fifth gas is transmitted to the breathing container through the patient-end respiratory system; and the third flow rate of the fifth gas delivered by the gas delivery branch is detected by the third flow sensor.

[0027] The processor is configured to calculate the tidal volume of a respiratory cycle based on the first flow rate, the second flow rate, and the third flow rate.

[0028] In the above-mentioned respiratory ventilation device, the patient-end respiratory system further includes: an inspiratory branch and an expiratory branch;

[0029] The inspiratory branch and the expiratory branch are both connected to the breathing container at one end of the common connection between the inspiratory branch and the expiratory branch. The gas delivery branch is connected to the inspiratory branch. The patient interface is located at the other end of the common connection between the inspiratory branch and the expiratory branch.

[0030] During the inhalation phase, the driving gas is transmitted to the inhalation branch through the driving gas interface, driving the first gas in the breathing container to the inhalation branch, and then transmitted to the patient interface by the inhalation branch.

[0031] During the exhalation phase, expiratory gas is received from the patient interface, transmitted to the breathing container through the expiratory branch, and excess mixed gas in the breathing container is discharged through the exhaust branch.

[0032] In the above-mentioned breathing ventilation device, the breathing container includes: an air mask, an air bag, and an air valve;

[0033] The airbag is disposed in the inner cavity of the air mask and connected to the patient's respiratory system. The airbag is a deformable structure and isolates the driving gas in the air mask from the first gas in the airbag.

[0034] The air intake branch is connected to the air cover, and the exhaust branch is connected to the air bag through the air valve;

[0035] During the inhalation phase, the driving gas is transmitted to the air hood through the air intake branch. The air bladder contracts and deforms under the pressure of the driving gas in the air hood, squeezing the first gas to be transmitted to the patient interface through the patient end breathing system, and the third gas is transmitted through the gas transmission branch and then transmitted to the patient interface through the patient end breathing system.

[0036] During the exhalation phase, expiratory gas is received from the patient interface, and the expiratory gas is transmitted to the air bag through the patient-end breathing system. The fifth gas is also received from the gas delivery branch and transmitted to the air bag through the patient-end breathing system.

[0037] The airbag expands and deforms under the action of the fifth gas and the exhaled gas, squeezing the driving gas inside the air hood and discharging it through the exhaust branch. When the pressure inside the airbag is greater than the pressure threshold of the air valve, the fifth gas and the exhaled gas inside the airbag are squeezed and discharged through the exhaust branch.

[0038] In the above-mentioned breathing ventilation device, the breathing container includes: an exchange chamber;

[0039] The exchange chamber is a hollow tubular structure. One end of the exchange chamber is connected to the air intake branch and the air exhaust branch, and the other end of the exchange chamber is connected to the patient's respiratory system.

[0040] During the inhalation phase, the driving gas is transmitted to the exchange chamber through the intake branch. The first gas in the exchange chamber is transmitted to the patient interface through the patient end breathing system under the pressure of the driving gas, and the third gas is transmitted through the gas transmission branch and transmitted to the patient interface through the patient end breathing system.

[0041] During the exhalation phase, expiratory gas is received from the patient interface, and the expiratory gas is transmitted to the exchange chamber through the patient-end breathing system. The fifth gas is also received from the gas delivery branch and transmitted to the exchange chamber through the patient-end breathing system.

[0042] The fifth gas and the exhaled gas in the exchange chamber drive the driving gas to mix, forming the mixed gas, and the mixed gas is discharged through the exhaust branch.

[0043] This invention also provides a breathing ventilation method, applied in the breathing ventilation device described above, the method comprising:

[0044] During the inhalation phase, driving gas is transmitted in the intake branch to drive the first gas in the breathing container to the patient-end breathing system, and then transmitted from the patient-end breathing system to the patient interface.

[0045] The first flow rate of the driving gas in the breathing container is detected by a flow monitor;

[0046] During the exhalation phase, expiratory gas is received from the patient interface and transmitted to the breathing container through the patient-end breathing system. Excess mixed gas in the breathing container is discharged through the exhaust branch.

[0047] The second flow rate of the mixed gas is detected by the flow monitor;

[0048] Based on the first flow rate and the second flow rate, calculate the tidal volume for one respiratory cycle.

[0049] In the above-described breathing and ventilation method, the flow monitor includes: a first flow sensor and a second flow sensor;

[0050] The first flow rate of the driving gas in the breathing container is detected by a flow monitor, including:

[0051] The first flow rate of the driving gas in the breathing container is detected by the first flow sensor;

[0052] The second flow rate of the mixed gas detected by the flow monitor includes:

[0053] The second flow rate of the mixed gas is detected by the second flow sensor.

[0054] In the above-described respiratory ventilation method, calculating the tidal volume for one respiratory cycle based on the first flow rate and the second flow rate includes:

[0055] The first flow rate is used as the inspiratory tidal volume, and the second flow rate is used as the expiratory tidal volume, thereby obtaining the tidal volume of one respiratory cycle.

[0056] In the above-described respiratory ventilation method, calculating the tidal volume for one respiratory cycle based on the first flow rate and the second flow rate includes:

[0057] Obtain the fresh gas flow rate over one respiratory cycle;

[0058] The inhaled tidal volume is obtained by adding the first flow rate to the fresh gas flow rate;

[0059] The expiratory tidal volume is obtained by subtracting the fresh gas flow rate from the second flow rate. The inspiratory tidal volume and the expiratory tidal volume are then added together to obtain the tidal volume of one respiratory cycle.

[0060] In the above-described respiratory ventilation method, the respiratory ventilation device includes: a third flow sensor; acquiring the fresh gas flow rate within one respiratory cycle includes:

[0061] The fresh gas flow rate is obtained by subtracting the first flow rate from the second flow rate and then averaging the results; or,

[0062] At the end of expiration, the third flow rate monitored by the third flow sensor is taken as the fresh gas flow rate; or,

[0063] The fresh gas flow rate is received from the front-end interface; or,

[0064] The fresh gas flow rate is determined based on the third flow rate detected by the third flow sensor and the functional relationship between the driving gas flow rate and the fresh gas flow rate.

[0065] In the above-described ventilation method, the patient-end respiratory system includes a gas delivery branch; the method further includes:

[0066] During the inhalation phase, the second gas is received through the fresh gas interface in the gas delivery branch, the second gas is transmitted to the evaporator in the gas delivery branch, and the third gas is carried out. The third gas is then transmitted to the patient interface via the patient-end respiratory system.

[0067] The third flow rate of the third gas delivered by the gas delivery branch is detected by the third flow sensor;

[0068] During the exhalation phase, a fourth gas is received through the fresh gas interface, the fourth gas is transmitted to the vaporizer, a fifth gas is carried out, and the fifth gas is transmitted to the breathing container through the patient-end respiratory system;

[0069] The third flow rate of the fifth gas delivered by the gas delivery branch is detected by the third flow sensor.

[0070] In the above-described respiratory ventilation method, calculating the tidal volume for one respiratory cycle based on the first flow rate and the second flow rate includes:

[0071] The tidal volume for one respiratory cycle is calculated based on the first flow rate, the second flow rate, and the third flow rate.

[0072] In the above-described respiratory ventilation method, calculating the tidal volume for one respiratory cycle based on the first flow rate, the second flow rate, and the third flow rate includes:

[0073] The inspiratory tidal volume is obtained by adding the first flow rate to the third flow rate;

[0074] The expiratory tidal volume is obtained by subtracting the third flow rate from the second flow rate.

[0075] The tidal volume of one respiratory cycle is obtained by adding the inspiratory tidal volume and the exhalation tidal volume.

[0076] This invention also provides an anesthesia machine, including: the breathing and ventilation device as described above.

[0077] This invention also provides a computer-readable storage medium storing executable ventilation instructions, which, when executed by the processor of an expiratory ventilation device, implement the breathing ventilation method described above.

[0078] In this embodiment of the invention, a flow monitor is installed on the side of the machine-side respiratory system, away from the patient-side respiratory system. During the inhalation phase, a first gas in the breathing container is driven by a driving gas to the patient-side respiratory system, which then transmits it to the patient interface. The flow monitor detects the first flow rate of the driving gas in the breathing container. During the exhalation phase, expiratory gas is received from the patient interface and transmitted to the breathing container through the patient-side respiratory system. Excess mixed gas in the breathing container is discharged through an exhaust branch, and the flow monitor detects the second flow rate of the mixed gas. The processor can calculate the tidal volume using the first and second flow rates. Because the flow monitor can monitor the gas flow rate in the machine-side respiratory system and takes into account the influence of different gas flow rates during inhalation and exhalation, the tidal volume obtained by this monitoring is highly accurate. Attached Figure Description

[0079] Figure 1 An exemplary structure of a respiratory ventilation device provided in an embodiment of the present invention. Figure 1 ;

[0080] Figure 2 An exemplary structure of a respiratory ventilation device provided in an embodiment of the present invention. Figure 2

[0081] Figure 3 An exemplary structure of a respiratory ventilation device provided in an embodiment of the present invention. Figure 3 ;

[0082] Figure 4 An exemplary structure of a respiratory ventilation device provided in an embodiment of the present invention. Figure 4 ;

[0083] Figure 5 An exemplary structure of a respiratory ventilation device provided in an embodiment of the present invention. Figure 5 ;

[0084] Figure 6 An exemplary structure of a respiratory ventilation device provided in an embodiment of the present invention. Figure 6 ;

[0085] Figure 7 An exemplary structure of a respiratory ventilation device provided in an embodiment of the present invention. Figure 7 ;

[0086] Figure 8 An exemplary structure of a respiratory ventilation device provided in an embodiment of the present invention. Figure 8 ;

[0087] Figure 9 A flowchart of an exemplary respiratory ventilation method provided in an embodiment of the present invention. Figure 1 ;

[0088] Figure 10 A flowchart of an exemplary respiratory ventilation method provided in an embodiment of the present invention. Figure 2 ;

[0089] Figure 11 A flowchart of an exemplary respiratory ventilation method provided in an embodiment of the present invention. Figure 3 ;

[0090] Figure 12 A flowchart of an exemplary respiratory ventilation method provided in an embodiment of the present invention. Figure 4 ;

[0091] Figure 13 A flowchart of an exemplary respiratory ventilation method provided in an embodiment of the present invention. Figure 5 ;

[0092] Figure 14 A flowchart of an exemplary respiratory ventilation method provided in an embodiment of the present invention. Figure 6 ;

[0093] Figure 15 A flowchart of an exemplary respiratory ventilation method provided in an embodiment of the present invention. Figure 7 ;

[0094] Figure 16 A flowchart of an exemplary respiratory ventilation method provided in an embodiment of the present invention. Figure 8 ;

[0095] Figure 17 A flowchart of an exemplary respiratory ventilation method provided in an embodiment of the present invention. Figure 9 . Detailed Implementation

[0096] The technical solutions of the present invention will be clearly and completely described below with reference to the accompanying drawings in the embodiments of the present invention.

[0097] To gain a more detailed understanding of the features and technical content of the embodiments of the present invention, the implementation of the embodiments of the present invention will be described in detail below with reference to the accompanying drawings. The accompanying drawings are for reference and illustration only and are not intended to limit the embodiments of the present invention.

[0098] This invention provides a respiratory ventilation method applied to a respiratory ventilation device. It should be noted that, in this embodiment, the respiratory ventilation method can be performed by a respiratory ventilation device or a respiratory ventilation apparatus. Figure 1 The structure of a breathing ventilation device provided in an embodiment of the present invention Figure 1 .

[0099] like Figure 1 As shown, the breathing ventilation device includes: a patient-side breathing system 1, a machine-side breathing system 2, a flow monitor 3, and a processor 4.

[0100] The machine-side breathing system 2 includes: an intake branch 21 for the inhalation phase, a breathing container 22, and an exhaust branch 23 for the exhalation phase.

[0101] Both the intake branch 21 and the exhaust branch 23 are connected to the breathing container 22 via the flow monitor 3, and the breathing container 22 is connected to the patient-end breathing system 1.

[0102] Processor 4 is connected to flow monitor 3; wherein,

[0103] During the inhalation phase, driving gas is transmitted through the intake branch 21 to drive the first gas in the breathing container 22 to the patient-end respiratory system 1, from which it is transmitted to the patient interface 10. The first flow rate of the driving gas in the breathing container 22 is detected by the flow monitor 3.

[0104] During the exhalation phase, expiratory gas is received from the patient interface 10 and transmitted to the breathing container 22 via the patient-end breathing system 1. Excess mixed gas in the breathing container 22 is discharged through the exhaust branch 23. The second flow rate of the mixed gas is detected by the flow monitor 3.

[0105] Processor 4 is used to calculate the tidal volume of a respiratory cycle based on the first flow rate and the second flow rate.

[0106] In this embodiment of the invention, during the inhalation phase, the intake branch 21 of the machine-side breathing system 2 transmits driving gas to the breathing container 22. The driving gas drives the first gas within the breathing container 22 to be transmitted to the patient interface 10 via the patient-side breathing system 1 connected to the breathing container 22. The patient interface 10 is connected to the patient, who inhales the first gas through the patient interface 10. In this embodiment of the invention, the flow monitor 3 is a bidirectional flow sensor, which detects the first flow rate of the driving gas. The flow monitor 3 transmits the value of the first flow rate to the processor 4, which can calculate the inspiratory tidal volume during the inhalation phase based on the first flow rate.

[0107] In this embodiment of the invention, during the exhalation phase, the patient exhales expiratory gas from the patient-end respiratory system 1 to the breathing container 22 via the patient interface 10. The expiratory gas is injected into the breathing container 22, compressing the mixed gas within the breathing container 22 out of it. The breathing container 22 is connected to an exhaust branch 23, through which the mixed gas is discharged. During the discharge of the mixed gas through the exhaust branch 23, the flow monitor 3 detects a second flow rate of excess mixed gas in the breathing container 22. The flow monitor 3 transmits this second flow rate to the processor 4, which can calculate the tidal volume during the exhalation phase. In this embodiment of the invention, the sum of the inspiratory and expiratory tidal volumes equals the tidal volume of one respiratory cycle.

[0108] In this embodiment of the invention, the processor 4 can be implemented by software, hardware, firmware, or a combination thereof. It can use circuits, one or more application-specific integrated circuits (ASICs), one or more general-purpose integrated circuits, one or more microprocessors, one or more programmable logic devices, or combinations of the aforementioned circuits or devices, or other suitable circuits or devices, thereby enabling the processor 4 to perform the corresponding functions of the breathing ventilation device. The flow monitor 3 can be a membrane flow sensor, a vane flow sensor, or a Karman vortex flow sensor; this embodiment of the invention does not impose any limitations.

[0109] In this embodiment of the invention, a pressure sensor 11 may also be installed on the patient-end respiratory system 1. The pressure sensor 11 is used to detect the pressure of the gas on the patient-end respiratory system 1. When the pressure of the gas on the patient-end respiratory system 1 is too high, the pressure sensor 11 sends a signal indicating that the pressure is too high to the processor 4, and the processor 4 issues an alarm through other devices.

[0110] In this embodiment of the invention, the first gas is a mixture of air and anesthetic gas. The mixture can be a driving gas. Alternatively, the mixture can be a mixture of driving gas, anesthetic gas, and exhaled gas.

[0111] In this embodiment of the invention, the driving gas can be air, and when the driving gas is input into the air intake branch 21 of the expiratory ventilation device, it can be input according to a fixed ratio. The fixed ratio is determined by the needs of the actual ventilation process, and this embodiment of the invention does not impose any restrictions.

[0112] It should be noted that in this embodiment of the invention, the processor 4 is connected to the flow monitor 3. For the sake of simplicity, the processor 4 is not shown in the illustrations of the following embodiments.

[0113] In this embodiment of the invention, a flow monitor 3 is provided on one side of the machine-side breathing system 2. During the inhalation phase, a first gas in the breathing container 22 is driven by a driving gas to the patient-side breathing system 1, and then transmitted from the patient-side breathing system 1 to the patient interface 10. The flow monitor 3 detects the first flow rate of the driving gas in the breathing container 22. During the exhalation phase, expiratory gas is received from the patient interface 10, transmitted through the patient-side breathing system 1 to the breathing container 22, and excess mixed gas in the breathing container 22 is discharged through the exhaust branch 23. The flow monitor 3 detects the second flow rate of the mixed gas. The processor 4 can calculate the tidal volume based on the first and second flow rates. Because the flow monitor 3 is located at the end of the machine breathing device and takes into account the influence of different gas flow rates during inhalation and exhalation, the tidal volume obtained by this monitoring is highly accurate.

[0114] In some embodiments of the present invention, such as Figure 2 As shown. The flow monitor 3 includes a first flow sensor 24 and a second flow sensor 25. Both the first and second flow sensors 24 and 25 are unidirectional flow sensors. The first flow sensor 24 is connected to the intake branch 21, and the second flow sensor 25 is connected to the exhaust branch 23. During the inhalation phase, the first flow sensor 24 detects the first flow rate of the driving gas in the breathing container 22. During the exhalation phase, the second flow sensor 25 detects the second flow rate of excess mixed gas in the breathing container. The first flow sensor 24 transmits the value of the first flow rate to the processor 4, and the second flow sensor 25 transmits the value of the second flow rate to the processor 4. The processor 4 can calculate the inspiratory tidal volume during the inhalation phase using the first flow rate. The processor 4 can calculate the expiratory tidal volume during the exhalation phase using the second flow rate. In this embodiment of the invention, the sum of the inspiratory and expiratory tidal volumes constitutes the tidal volume of one respiratory cycle.

[0115] In some embodiments of the present invention, a fifth one-way valve 26 is also provided on the air intake branch 21. The fifth one-way valve 26 ensures that the driving gas can only flow to the breathing container 22.

[0116] It should be noted that the location of the first flow sensor 24 on the intake branch 21 is not limited in this embodiment of the invention, and the location of the second flow sensor 25 on the exhaust branch 23 is not limited in this embodiment of the invention. Figure 2 This is just one example setup.

[0117] In some embodiments of the present invention, such as Figure 3 As shown. The breathing ventilation device further includes: a first one-way valve 262 and a second one-way valve 261. The flow monitor 3 includes: a first flow sensor 24 and a second flow sensor 25. Both the first flow sensor 24 and the second flow sensor 25 are one-way flow sensors. The first one-way valve 262 is used to transmit the driving gas to the breathing container 22. The second one-way valve 261 is used to transmit the mixed gas to the exhaust branch 23. The intake branch 21 and the exhaust branch 23 are both connected to the breathing container 22 through the first flow sensor 24, the first one-way valve 262, the second flow sensor 25, and the second one-way valve 261. The first one-way valve 262 is connected to the first flow sensor 24, and the second one-way valve 261 is connected to the second flow sensor 25.

[0118] During the inhalation phase, the driving gas flows to the breathing container 22 through the first one-way valve 262 and the first flow sensor 24. The first flow sensor 24, connected to the first one-way valve 262, detects the first flow rate of the driving gas in the breathing container 22. During the exhalation phase, excess mixed gas in the exhalation container 22 is discharged from the exhaust branch through the second one-way valve 261 and the second flow sensor 25. The second flow sensor 25 detects the second flow rate of the mixed gas discharged through the exhaust branch 23. The first flow sensor 24 transmits the value of the first flow rate to the processor 4, and the second flow sensor 25 transmits the value of the second flow rate to the processor 4. Similarly, the processor 4 can calculate the inspiratory tidal volume during the inhalation phase using the first flow rate. The processor 4 can calculate the expiratory tidal volume during the exhalation phase using the second flow rate. In this embodiment of the invention, the sum of the inspiratory tidal volume and the expiratory tidal volume equals the tidal volume of one respiratory cycle.

[0119] It should be noted that the placement of the first flow sensor 24, the first one-way valve 262, the second flow sensor 25, and the second one-way valve 261 on the intake branch 21 and the exhaust branch 23 is not limited in this embodiment of the invention. Figure 3 This is just one example setup.

[0120] In some embodiments of the present invention, such as Figure 4 As shown. The breathing ventilation device also includes: a gas delivery branch 5. The gas delivery branch 5 is equipped with a third flow sensor 53, a fresh gas interface 51, and an evaporator 52.

[0121] During the inhalation phase, a second gas is received through the fresh gas interface 51 and transmitted to the evaporator 52. The second gas carries away a third gas from the evaporator 52. The third gas is transmitted to the patient interface 10 via the patient-side respiratory system 1. The third flow rate of the third gas delivered by the gas delivery branch 5 is detected by the third flow sensor 53.

[0122] During the exhalation phase, a fourth gas is received through the fresh gas interface 51 and delivered to the evaporator 52. The fourth gas carries away a fifth gas from the evaporator 52. The fifth gas is then delivered to the breathing container 22 via the patient-end breathing system 1. The third flow sensor 53 detects the third flow rate of the fifth gas delivered through the gas delivery branch 1. The third flow sensor 53 transmits the values ​​of the third flow rate of the third gas and the third flow rate of the fifth gas to the processor 4. The processor 4 calculates the tidal volume for one respiratory cycle based on the first flow rate, the second flow rate, and the third flow rate.

[0123] In this embodiment of the invention, during the inhalation phase, the intake branch 21 of the machine-side breathing system 2 delivers driving gas to the breathing container 22. The driving gas drives a first gas within the breathing container 22 to be delivered to the patient interface 10 via the patient-side breathing system 1 connected to the breathing container 22, where the patient inhales the first gas. Simultaneously, a second gas is received through the fresh gas interface 51 and delivered to the evaporator 52. The second gas carries away a third gas from the evaporator 52, which is then delivered to the patient interface 10 via the patient-side breathing system 1. In this embodiment, a first flow sensor 24 detects the first flow rate of the driving gas entering the breathing container 22. A third flow sensor 53 detects the third flow rate of the third gas delivered by the gas delivery branch 5. The first flow sensor 24 sends the value of the first flow rate to the processor 4, and the third flow sensor 53 sends the value of the third flow rate of the third gas to the processor 4. The processor 4 can calculate the inspiratory tidal volume during the inhalation phase using the first and third flow rates. For example, the processor 4 can add the first and third flow rates together to calculate the inspiratory tidal volume during the inhalation phase.

[0124] In this embodiment of the invention, during the exhalation phase, the patient exhales gas from the patient-end respiratory system 1 through the patient interface 10 and transfers it to the breathing container 22. Simultaneously, the gas delivery branch 5 receives a fourth gas through the fresh gas interface 51, transmits the fourth gas to the evaporator 52, and the fourth gas carries out a fifth gas from within the evaporator 52. The fifth gas is then transmitted to the breathing container 22 via the patient-end respiratory system 1. The exhaled gas and the fifth gas simultaneously expel the mixed gas within the breathing container 22. If the breathing container 22 is a structure with an airbag inside the air mask, the exhaled gas is injected into the airbag, causing it to inflate and expel the driving gas outside the airbag and inside the air mask from the breathing container, which is then discharged through the exhaust branch 23. When the air pressure inside the airbag reaches a certain level, the excess mixed gas in the airbag is discharged through the exhaust branch 23. If the exhalation container 22 is a hollow tubular structure, the exhaled gas and the fifth gas expel the excess mixed gas from the exhalation container 22 and discharge it through the exhaust branch 23. The machine-mounted breathing system 2 detects the second flow rate of the mixed gas discharged from the exhaust branch 23 via the second flow sensor 25. It also detects the third flow rate of the fifth gas delivered by the gas delivery branch 5 via the third flow sensor 53. The second flow sensor 25 sends the value of the second flow rate to the processor 4, and the third flow sensor 53 sends the value of the third flow rate of the fifth gas to the processor 4. The processor 4 can calculate the expiratory tidal volume during the expiratory phase by subtracting the third flow rate from the second flow rate.

[0125] It should be noted that during the inhalation phase, processor 4 adds the first flow rate to the third flow rate of the third gas to obtain the inspiratory tidal volume during the inhalation phase. During the exhalation phase, processor 4 subtracts the third flow rate of the fifth gas from the second flow rate to obtain the expiratory tidal volume during the exhalation phase. In this embodiment of the invention, the sum of the inspiratory tidal volume and the expiratory tidal volume equals the tidal volume of one respiratory cycle.

[0126] In this embodiment of the invention, the second and fourth gases are air or oxygen. The third and fifth gases are mixtures of air or oxygen with anesthetic gases; this embodiment of the invention does not impose any limitations.

[0127] In this embodiment of the invention, the third flow sensor 53 can be omitted from the breathing ventilation device. The processor 4 can calculate the third flow rate using the first flow sensor 24 and the second flow sensor 25. The processor 4 obtains the third flow rate by averaging the second flow rate of the second flow sensor 25 during the exhalation phase with the first flow rate of the first flow sensor 24 during the inhalation phase. In this embodiment of the invention, the processor 4 can obtain the third flow rate by subtracting the first flow rate of the first flow sensor 24 during the inhalation phase from the second flow rate of the second flow sensor 25 during the exhalation phase and dividing by 2.

[0128] In some embodiments of the present invention, such as Figure 5As shown. The patient-end respiratory system 1 also includes an inspiratory branch 16 and an expiratory branch 15. Both the inspiratory branch 16 and the expiratory branch 15 are connected to the breathing container 22 at one end of the common connection between the inspiratory branch 16 and the expiratory branch 15. A gas delivery branch 5 is connected to the inspiratory branch 16, and the patient interface 10 on the patient-end respiratory system 1 is located at the other end of the common connection between the inspiratory branch 16 and the expiratory branch 15.

[0129] During the inhalation phase, driving gas is drawn in through the intake branch 21 and transported into the breathing container 22 via the intake branch 21. The driving gas drives the first gas in the breathing container 22 to the inhalation branch 16. The first gas is then transported to the patient interface 10 via the inhalation branch 16.

[0130] During the exhalation phase, expiratory gas is received from the patient interface 10 and transmitted to the breathing vessel 22 via the expiratory branch 15. The expiratory gas compresses excess mixed gas within the breathing vessel 22 and is expelled through the exhaust branch 23 connected to the breathing vessel 22.

[0131] In this embodiment of the invention, during the inhalation phase, the intake branch 21 of the machine-side breathing system 2 delivers driving gas to the breathing container 22. The driving gas drives a first gas within the breathing container 22 to be delivered to the patient interface 10 via the inhalation branch 16 connected to the breathing container 22, where the patient inhales the first gas. Simultaneously, a second gas is received through the fresh gas interface 51 and delivered to the evaporator 52. The second gas carries away a third gas from the evaporator 52, which is then delivered to the patient interface 10 via the inhalation branch 16. In this embodiment, a first flow sensor 24 detects the first flow rate of the driving gas in the breathing container 22. A third flow sensor 53 detects the third flow rate of the third gas delivered by the gas delivery branch 5. The first flow sensor 24 sends the value of the first flow rate to the processor 4, and the third flow sensor 53 sends the value of the third flow rate of the third gas to the processor 4. The processor 4 can calculate the inhalation tidal volume during the inhalation phase by adding the first and third flow rates.

[0132] In this embodiment of the invention, during the exhalation phase, the patient exhales gas from the exhalation branch 15 through the patient interface 10 to the breathing container 22. For example, the exhaled gas passes through the air mask 27 of the breathing container 22. Figure 6 The driving gas inside the breathing container 22 is expelled from the breathing container 22. The exhaust branch 23 of the breathing container 22 is connected to the air bladder 28 of the breathing container 22. Figure 6Excess mixed gas in the air (as shown) is also expelled from the exhaust branch 23 by the compression of the exhaled gas. Simultaneously, the gas delivery branch 5 receives the fourth gas through the fresh gas interface 51, transmits the fourth gas to the evaporator 52, and the fourth gas carries out the fifth gas from the evaporator. The fifth gas is then transmitted to the breathing container 22 via the inhalation branch 16. The patient-side respiratory system 2 detects the second flow rate of the mixed gas discharged from the exhaust branch 23 via the second flow sensor 25, and the third flow rate of the fifth gas delivered by the gas delivery branch 5 via the third flow sensor 53. The second flow sensor 25 sends the value of the second flow rate to the processor 4, and the third flow sensor 53 sends the value of the third flow rate of the fifth gas to the processor 4. The processor 4 can calculate the tidal volume of the exhalation phase by subtracting the third flow rate of the fifth gas from the second flow rate.

[0133] In this embodiment of the invention, since the gas delivery branch 5 delivers the third gas and the fifth gas during both the inhalation and exhalation phases, the flow rates of the third gas and the fifth gas are the same, and both are the third flow rate.

[0134] It should be noted that, during the inhalation phase, processor 4 adds the first flow rate to the third flow rate of the third gas to obtain the inspiratory tidal volume. During the exhalation phase, processor 4 subtracts the third flow rate of the fifth gas from the second flow rate to obtain the expiratory tidal volume. In this embodiment of the invention, the sum of the inspiratory and expiratory tidal volumes constitutes the tidal volume of one respiratory cycle.

[0135] It should be noted that a filter 13 can be installed on the inspiratory branch 16. During the inhalation phase, the filter 13 is used to filter impurities in the first gas, and during the exhalation phase, the filter 13 is used to filter impurities in the fifth gas. A third one-way valve 14 is also installed on the inspiratory branch 16, and a fourth one-way valve 12 is installed on the expiratory branch 15. The third one-way valve 14 ensures that the gas in the inspiratory branch 16 can only be transmitted towards the patient interface 10. The fourth one-way valve 12 ensures that the gas in the expiratory branch 15 can only be transmitted from the patient interface 10 towards the breathing vessel 22.

[0136] In some embodiments of the present invention, such as Figure 6 As shown. The breathing container 22 includes: an air mask 27, an air bag 28, and an air valve 29; the air bag 28 is disposed in the inner cavity of the air mask 27 and is connected to the patient-end breathing system 1. The air bag 28 has a deformable structure and isolates the driving gas in the air mask 27 from the first gas in the air bag; the air inlet branch 21 is connected to the air mask 27, and the air outlet branch 23 is connected to the air bag 28 through the air valve 29; the air inlet branch 21 is connected to the air mask 27, and the air outlet branch 23 is connected to the air bag 28 through the air valve 29.

[0137] During the inhalation phase, the driving gas is transmitted to the air mask 27 through the air intake branch 21. The air bag 28 contracts and deforms under the pressure of the driving gas inside the air mask 27, squeezing the first gas to be transmitted to the patient interface 10 through the patient end breathing system 1, and the third gas is transmitted through the gas transmission branch 5 and then transmitted to the patient interface 10 through the patient end breathing system 1.

[0138] During the exhalation phase, expiratory gas is received from the patient interface 10, transmitted to the air bag 28 through the patient-end respiratory system 1, and a fifth gas is received from the gas delivery branch 5, transmitted to the air bag 28 through the patient-end respiratory system 1.

[0139] The airbag 28 expands and deforms under the action of the fifth gas and the exhaled gas, squeezing the driving gas in the air cover 27 and discharging it through the exhaust branch 23. When the pressure in the airbag 28 is greater than the pressure threshold of the air valve, the fifth gas and the exhaled gas in the airbag 28 are squeezed and discharged through the exhaust branch 23.

[0140] In this embodiment of the invention, during the inhalation phase, the intake branch 21 of the machine-mounted respiratory system 2 delivers driving gas to the air hood of the breathing container 22. The airbag 28 contracts and deforms under the pressure of the driving gas within the air hood 27, compressing the first gas. The first gas is delivered to the patient interface 10 via the inhalation branch 16 connected to the airbag 28, and the patient inhales the first gas through the patient interface 10. Simultaneously, a second gas is received through the fresh gas interface 51 and delivered to the evaporator 52. The second gas carries away a third gas from the evaporator 52, and the third gas is delivered to the patient interface 10 via the inhalation branch 16. In this embodiment of the invention, the machine-mounted respiratory system 2 detects the first flow rate of the driving gas in the exhalation container 22 via the first flow sensor 24, and detects the third flow rate of the third gas delivered by the gas delivery branch 5 via the third flow sensor 53. The first flow sensor 24 sends the value of the first flow rate to the processor 4, and the third flow sensor 53 sends the value of the third flow rate of the third gas to the processor 4. The processor 4 can calculate the inhalation tidal volume during the inhalation phase using the first and third flow rates.

[0141] In this embodiment of the invention, during the exhalation phase, the patient exhales gas through the patient interface 10 from the exhalation branch 15 to the air bag 28 of the breathing container 22. Simultaneously, a fourth gas is received through the fresh gas interface 51 and transmitted to the evaporator 52. The fourth gas carries away a fifth gas from the evaporator 52, and the fifth gas is transmitted to the air bag 28 via the inhalation branch 16. The air bag 28 expands under the action of the exhaled gas and the fifth gas, first forcing the driving gas in the air mask 27 of the breathing container 22 from the connecting branch 31 connected to the air mask 27 into the exhaust branch 23. The driving gas is then discharged from the air mask 27 through the exhaust branch 23. When the air bag 28 expands to the top of the air mask 27 and the internal pressure is greater than the pressure threshold of the valve 29, the exhaled gas and the fifth gas in the air bag 28 are discharged through the exhaust branch 23 connected to the valve 29. A second flow rate of the mixed gas discharged from the exhaust branch 23 is detected by a second flow sensor 24, wherein the mixed gas includes the fifth gas, the driving gas, and the exhaled gas. The third flow rate of the fifth gas delivered by the gas delivery branch 5 is detected by the third flow sensor 53. The second flow sensor 25 sends the value of the second flow rate to the processor 4, and the third flow sensor 53 sends the value of the third flow rate of the fifth gas to the processor 4. The processor can calculate the tidal volume of the exhalation phase using the second and third flow rates.

[0142] In this embodiment of the invention, the processor 4 can measure the third flow rate at the end of the exhalation phase, since the patient's exhalation has completely ended at this stage. At this time, the air bag 28 has risen to its maximum position. The fifth gas entering the air bag 28 will mix with the gas inside the air bag 28. When the pressure inside the air bag 28 exceeds the pressure threshold of the valve 29, the mixed gas inside the air bag 28 will overflow from the valve 29. Therefore, at the end of exhalation, the third flow rate can be obtained by monitoring the data from the second flow sensor 25 at the end of the breathing container 22 in a point-measurement manner.

[0143] In some embodiments of the present invention, such as Figure 7As shown. The breathing container 22 includes: an exchange chamber 30; the exchange chamber is a hollow tubular structure, one end of the exchange chamber 30 is connected to an inlet branch 21 and an exhaust branch 23, and the other end of the exchange chamber 30 is connected to a patient-end breathing system 1; during the inhalation phase, the driving gas is transmitted to the exchange chamber 30 through the inlet branch 21, and the first gas in the exchange chamber 30 is transmitted to the patient interface 10 through the patient-end breathing system 1 under the pressure of the driving gas. At the same time, a third gas is transmitted through the gas transmission branch 5 and transmitted to the patient interface 10 through the patient-end breathing system 1; during the exhalation phase, expiratory gas is received from the patient interface 10 and transmitted to the exchange chamber 30 through the patient-end breathing system 1, and a fifth gas is received from the gas transmission branch 5 and transmitted to the exchange chamber 30 through the patient-end breathing system 1; the exchange chamber 30 discharges excess mixed gas through the exhaust branch 23 under the pressure of the fifth gas and the expiratory gas.

[0144] In this embodiment of the invention, the exchange cavity is a hollow, straight tubular structure.

[0145] It should be noted that the exhaled gas mixture may include: exhaled gas, fifth gas, and driving gas. The exhaled gas mixture may also include: driving gas.

[0146] In some embodiments of the present invention, such as Figure 8 As shown. The breathing container 22 includes an exchange chamber 30. The exchange chamber is an inverted U-shaped tubular structure with a hollow interior. In other embodiments, the exchange chamber may also be a tubular structure of other shapes with a hollow interior.

[0147] In this embodiment of the invention, a first flow sensor 24 and a second flow sensor 25 are disposed on one side of the machine-side breathing system 2, and the first flow sensor 24 and the second flow sensor 25 are located away from the patient. During the inhalation phase, a first gas in the breathing container 22 is driven by a driving gas to the patient-side breathing system 1, and then transmitted by the patient-side breathing system 1 to the patient interface 10. The first flow sensor 24 detects the first flow rate of the driving gas in the breathing container 22. Simultaneously, a third gas is transmitted through the gas transmission branch 5, and then transmitted through the patient-side breathing system 1 to the patient interface 10. The third flow sensor 53 detects the third flow rate of the third gas. During the exhalation phase, expiratory gas is received from the patient interface 10 and transmitted to the breathing container 22 through the patient-end respiratory system. Simultaneously, a fifth gas is received from the gas delivery branch 5 and transmitted to the breathing container 22 through the patient-end respiratory system 1. Under the action of the fifth gas and the expiratory gas, the breathing container 22 discharges excess mixed gas through the exhaust branch 23. The second flow rate of the discharged mixed gas is detected by the second flow sensor 25, and the fourth flow rate of the fifth gas delivered by the gas delivery branch 5 is detected by the third flow sensor 53. The processor 4 can calculate the tidal volume based on the first flow rate, the second flow rate, the third flow rate, and the fourth flow rate. Since the first flow sensor 24 and the second flow sensor 25 are located in the machine-end respiratory system 2, and the influence of different gas flow rates during inhalation and exhalation is taken into account, the tidal volume obtained by this monitoring is highly accurate.

[0148] Based on the aforementioned structure of the breathing ventilation device, Figure 9 This is a schematic flowchart illustrating a respiratory ventilation method applied in a respiratory ventilation device, as provided in an embodiment of the present invention. Figure 9 As shown, the breathing and ventilation method mainly includes the following steps:

[0149] S01. During the inhalation phase, driving gas is transmitted in the intake branch to drive the first gas in the breathing container to the patient-end breathing system, and then transmitted from the patient-end breathing system to the patient interface.

[0150] In this embodiment of the invention, during the inhalation phase, the intake branch transmits driving gas to the breathing container. The driving gas drives the first gas within the breathing container to be transmitted to the patient interface through the patient-end breathing system connected to the breathing container, and the patient inhales the first gas through the patient interface.

[0151] In this embodiment of the invention, the patient-end respiratory system may include an inspiratory branch, and the driving gas drives the first gas in the breathing container to be transmitted to the patient interface through the inspiratory branch connected to the breathing container.

[0152] In this embodiment of the invention, the first gas is a mixture of air and anesthetic gas. In this embodiment of the invention, the driving gas can be air. When the driving gas is input into the inlet branch of the expiratory ventilation device, it can be input according to a fixed ratio. The fixed ratio is determined by the needs of the actual ventilation process, and this embodiment of the invention does not impose any limitations.

[0153] S02. Detect the first flow rate of the driving gas in the breathing container using a flow monitor.

[0154] In this embodiment of the invention, the flow monitor is a bidirectional flow sensor that detects the first flow rate of the driving gas. The flow monitor can be located at the intersection of the intake branch and the exhaust branch. The flow monitor can be a diaphragm flow sensor, a vane flow sensor, or a Karman vortex flow sensor; this embodiment of the invention does not impose any limitations.

[0155] S03. During the exhalation phase, expiratory gas is received from the patient interface and transmitted to the breathing container through the patient-end breathing system. Excess mixed gas in the breathing container is discharged through the exhaust branch.

[0156] In this embodiment of the invention, during the exhalation phase, the patient exhales gas from the patient-end respiratory system and transfers it to the breathing container via the patient interface. The exhaled gas forces the mixed gas inside the breathing container out of the container, and the mixed gas is discharged through the exhaust branch of the breathing container.

[0157] In this embodiment of the invention, the mixed gas can be a driving gas, or it can be a mixture of driving gas, anesthetic gas and exhaled gas.

[0158] In this embodiment of the invention, the patient-end respiratory system may include an expiratory branch, through which the patient's exhaled gas is transmitted from the expiratory branch to the breathing container via a patient interface.

[0159] S04. Detect the second flow rate of the mixed gas using a flow monitor.

[0160] In this embodiment of the invention, a second flow rate of the mixed gas discharged from the exhaust branch is detected by a flow monitor.

[0161] In this embodiment of the invention, the flow monitor may include two flow sensors, which respectively detect a first flow rate and a second flow rate.

[0162] S05. Based on the first flow rate and the second flow rate, calculate the tidal volume for one respiratory cycle.

[0163] In this embodiment of the invention, the processor uses the first flow rate as the inspiratory tidal volume. The processor uses the second flow rate as the expiratory tidal volume. The processor adds the first and second flow rates to obtain the tidal volume for one respiratory cycle.

[0164] In this embodiment of the invention, the processor adds a fixed value to a first flow rate to obtain the inspiratory tidal volume. The processor subtracts the fixed value from a second flow rate to obtain the expiratory tidal volume. The processor adds the calculated first and second flow rates to obtain the tidal volume for one respiratory cycle. The fixed value can be the flow rate of fresh gas inhaled into the lungs or entering the breathing container during breathing.

[0165] In this embodiment of the invention, the respiratory ventilation device may include a processor. The respiratory ventilation device uses the processor to add a first flow rate and a second flow rate to obtain the tidal volume of one respiratory cycle.

[0166] In embodiments of the present invention, the processor can be implemented by software, hardware, firmware or a combination thereof, and can use circuits, one or more application-specific integrated circuits (ASICs), one or more general-purpose integrated circuits, one or more microprocessors, one or more programmable logic devices, or a combination of the aforementioned circuits or devices, or other suitable circuits or devices, so that the processor can perform the corresponding steps of the breathing ventilation method.

[0167] In this embodiment of the invention, during the inhalation phase, a first gas in the breathing container is driven by a driving gas to the patient-end breathing system, which then transmits it to the patient interface. A flow monitor detects the first flow rate of the driving gas in the breathing container. During the exhalation phase, expiratory gas is received from the patient interface and transmitted to the breathing container via the patient-end breathing system. Excess mixed gas in the breathing container is discharged through an exhaust branch, and a flow monitor detects the second flow rate of the mixed gas. The flow monitor sends the values ​​of the first and second flow rates to the processor, which can calculate the tidal volume using the first and second flow rates. Because the flow monitor can monitor gas flow in the machine-end breathing system and takes into account the influence of different gas flow rates during inhalation and exhalation, the tidal volume obtained through this monitoring is highly accurate.

[0168] In some embodiments, see Figure 10 , Figure 10 This is a schematic diagram of an optional process for the respiratory ventilation method provided in an embodiment of the present invention. Figure 9 The S02 shown can be implemented through S06, which will be explained in conjunction with each step.

[0169] S06, the first flow rate of the driving gas in the breathing container is detected by the first flow sensor.

[0170] In this embodiment of the invention, the flow monitor includes a first flow sensor and a second flow sensor. Both the first and second flow sensors are unidirectional flow sensors. The first flow sensor is connected to the intake branch; during the inhalation phase, the first flow sensor detects the first flow rate of the driving gas in the breathing container.

[0171] In this embodiment of the invention, the intake branch and exhaust branch of the machine-side breathing system are both connected to the breathing container through a first flow sensor and a second flow sensor; during the inhalation phase, the first flow rate of the driving gas in the breathing container is detected by the first flow sensor.

[0172] The first flow sensor can be connected to the first check valve, and the second flow sensor can be connected to the second check valve; the first check valve is used to transmit the driving gas to the breathing container; the second check valve is used to transmit the mixed gas to the exhaust branch.

[0173] In some embodiments, see Figure 10 , Figure 10 This is a schematic diagram of an optional process for a respiratory ventilation method provided in an embodiment of the present invention. Figure 9 The steps S04-S05 shown can be implemented through S07-S08, which will be explained in conjunction with each step.

[0174] S07, the second flow rate of the mixed gas is detected by the second flow sensor.

[0175] In this embodiment of the invention, the flow monitor includes a first flow sensor and a second flow sensor. Both the first and second flow sensors are unidirectional flow sensors. The second flow sensor is connected to the exhaust branch; during the exhalation phase, the second flow sensor detects the second flow rate of the gas mixture.

[0176] S08, the first flow rate is used as the inspiratory tidal volume, and the second flow rate is used as the expiratory tidal volume, thus obtaining the tidal volume of one respiratory cycle.

[0177] In this embodiment of the invention, the processor uses the first flow rate as the inspiratory tidal volume. The processor uses the second flow rate as the expiratory tidal volume. The processor adds the first and second flow rates to obtain the tidal volume for one respiratory cycle.

[0178] In this embodiment of the invention, during the inhalation phase, a first gas in the breathing container is driven by a driving gas to the patient-end breathing system, which then transmits it to the patient interface. A first flow sensor detects the first flow rate of the driving gas in the breathing container. During the exhalation phase, expiratory gas is received from the patient interface and transmitted to the breathing container via the patient-end breathing system. Excess mixed gas in the breathing container is discharged through an exhaust branch, and a second flow sensor detects the second flow rate of the mixed gas. The first flow sensor sends the value of the first flow rate to the processor, and the second flow sensor sends the value of the second flow rate to the processor. The processor can calculate the tidal volume using the first and second flow rates. Because the flow monitor can monitor gas flow in the machine-end breathing system and takes into account the influence of different gas flow rates during inhalation and exhalation, the accuracy of the tidal volume obtained by this monitoring is high.

[0179] In some embodiments, see Figure 11 , Figure 11 This is a schematic diagram of an optional process for a respiratory ventilation method provided in an embodiment of the present invention. Figure 9 The shown S05 can be implemented through S09-S11, which will be explained in conjunction with each step.

[0180] S09, obtain the fresh gas flow rate within one breathing cycle.

[0181] In this embodiment of the invention, the flow rate of fresh gas within a breathing cycle can be detected by a flow sensor.

[0182] In this embodiment of the invention, the flow rate of fresh gas in one respiratory cycle can be the difference between the flow rate of fresh gas entering the patient's lungs during inhalation and the flow rate of fresh gas entering the breathing container during exhalation.

[0183] In this embodiment of the invention, the flow rate of fresh gas in one breathing cycle can be manually input via a keyboard or input device on the breathing ventilation device.

[0184] S10 uses the first flow rate plus the fresh gas flow rate to obtain the inhaled tidal volume.

[0185] In this embodiment of the invention, the processor adds the first flow rate and the fresh gas flow rate to obtain the inhaled tidal volume.

[0186] In this embodiment of the invention, the first flow rate is the flow rate of the breathing container inputting the first gas into the patient interface, and the fresh gas flow rate is the flow rate of the third gas inhaled by the patient during inhalation.

[0187] S11, the expiratory tidal volume is obtained by subtracting the fresh gas flow rate from the second flow rate. The inspiratory tidal volume and the expiratory tidal volume are added together to obtain the tidal volume of one respiratory cycle.

[0188] In this embodiment of the invention, the processor subtracts the fresh gas flow rate from the second flow rate to obtain the expiratory tidal volume. The processor adds the inspiratory tidal volume and the expiratory tidal volume to obtain the tidal volume over one cycle.

[0189] In this embodiment of the invention, the second flow rate is the flow rate of the mixed gas discharged from the breathing container when the patient exhales. The fresh gas flow rate is the flow rate of the fifth gas entering the breathing container when the patient exhales.

[0190] In this embodiment of the invention, a flow monitor is installed on the side of the machine-side respiratory system, away from the patient. During inhalation, a first gas in the breathing container is driven by a driving gas to the patient-side respiratory system, and then transmitted from the patient-side respiratory system to the patient interface. The flow monitor detects the first flow rate of the driving gas in the breathing container, while a flow sensor detects the flow rate of the new gas. During exhalation, expiratory gas is received from the patient interface and transmitted to the breathing container through the patient-side respiratory system. Simultaneously, new gas is received, and the mixed gas in the breathing container expels excess mixed gas under the action of the new and expiratory gas. The flow monitor detects the second flow rate of the expelled mixed gas, and the flow sensor detects the flow rate of the new gas. The processor can calculate the tidal volume using the first flow rate, the second flow rate, and the flow rate of the new gas during the respiratory phase. Because the flow monitor can monitor the gas flow rate within the machine-side respiratory system and takes into account the influence of different gas flow rates during inhalation and exhalation, the tidal volume obtained by this monitoring is highly accurate.

[0191] In some embodiments, see Figure 12 , Figure 12 This is a schematic diagram of an optional process for a respiratory ventilation method provided in an embodiment of the present invention. Figure 11 The shown S09 can be implemented through S12, which will be explained in conjunction with each step.

[0192] S12, the fresh gas flow rate is obtained by subtracting the first flow rate from the second flow rate and then averaging the results.

[0193] In this embodiment of the invention, during the inhalation phase, the first flow rate is simply the flow rate of the first gas inhaled by the patient, while the second gas flow rate during exhalation includes both the exhaled gas flow rate and the fresh gas flow rate. The processor subtracts the first flow rate from the second flow rate to obtain the sum of the fresh gas flow rates during the patient's inhalation and exhalation. Since the fresh gas flow rates during the patient's inhalation and exhalation are the same, the processor can obtain the fresh gas flow rate during either the inhalation or exhalation phase by dividing the sum of the fresh gas flow rates by 2.

[0194] In some embodiments, see Figure 13 , Figure 13 This is a schematic diagram of an optional process for a respiratory ventilation method provided in an embodiment of the present invention. Figure 11 The shown S09 can be implemented through S13, which will be explained in conjunction with each step.

[0195] S13, at the end of exhalation, the third flow rate monitored by the third flow sensor is used as the fresh gas flow rate.

[0196] In this embodiment of the invention, during the breathing phase, since the actual flow rate of fresh gas entering the ventilation device is very small, and the patient's exhalation has completely ended at the end of the exhalation phase, the cuff has risen to its maximum height. Any fresh gas continuing to enter the cuff will mix with the gas inside the cuff. When the pressure inside the cuff exceeds the pressure threshold of the valve connected to the cuff, all the mixed gas inside the cuff overflows from the valve. The flow rate of the gas overflowing from the valve is the same as the flow rate of fresh gas. Therefore, at the end of exhalation, the new gas flow rate can be obtained from the data monitored by the third flow sensor in a point-measurement manner.

[0197] In some embodiments, see Figure 14 , Figure 14 This is a schematic diagram of an optional process for a respiratory ventilation method provided in an embodiment of the present invention. Figure 11 The shown S09 can be implemented through S14, which will be explained in conjunction with each step.

[0198] S14 receives the fresh gas flow rate from the front-end interface.

[0199] In this embodiment of the invention, the front-end interface of the breathing ventilation device can be displayed on a touch screen. The breathing ventilation device may also include an input keyboard. The operator can input the fresh gas flow rate value via the input keyboard or touch screen. The processor obtains the fresh gas flow rate based on the input value. Therefore, the input value is the fresh gas flow rate.

[0200] In some embodiments, see Figure 15 , Figure 15 This is a schematic diagram of an optional process for a respiratory ventilation method provided in an embodiment of the present invention. Figure 11 S09 shown can be implemented through S15, and will be explained in conjunction with each step.

[0201] S15, based on the third flow rate detected by the third flow sensor and the functional relationship between the driving gas flow rate and the fresh gas flow rate, determine the fresh gas flow rate.

[0202] In this embodiment of the invention, the working time during the inhalation and exhalation phases is the same, and the intake volumes of the driving gas inlet and the fresh gas inlet also have a corresponding functional relationship. Therefore, the processor can determine the new gas flow rate through the functional relationship between the driving gas flow rate and the fresh gas flow rate.

[0203] In this embodiment of the invention, the driving gas flow rate can be N times the fresh gas flow rate. N can be 1, 2, 10, or 0.2, and the specific value is not limited.

[0204] Based on the aforementioned structure of the breathing ventilation device, Figure 16 This is a schematic flowchart illustrating a respiratory ventilation method applied in a respiratory ventilation device, as provided in an embodiment of the present invention. Figure 16 As shown, the breathing and ventilation method mainly includes the following steps:

[0205] S16, during the inhalation phase, the driving gas is transmitted in the intake branch, driving the first gas in the breathing container to the patient-end breathing system, which then transmits it to the patient interface. The second gas is received through the fresh gas interface in the gas delivery branch, and the second gas is transmitted to the evaporator in the gas delivery branch, carrying out the third gas. The third gas is then transmitted to the patient interface through the breathing gas branch.

[0206] In this embodiment of the invention, during the inhalation phase, the inhalation branch of the machine-mounted breathing system transmits driving gas to the breathing container. The driving gas drives a first gas within the breathing container to be transmitted to the patient interface via an inhalation branch connected to the breathing container, where the patient inhales the first gas. Simultaneously, a second gas is received through a fresh gas interface and transmitted to the evaporator. The second gas carries away a third gas from the evaporator, which is then transmitted to the patient interface via the inhalation branch.

[0207] In this embodiment of the invention, the second gas can be air. The third gas can be a mixture of anesthetic gas and air.

[0208] S17, the first flow rate of the driving gas in the breathing container is detected by the first flow sensor, and the third flow rate of the third gas delivered by the gas delivery branch is detected by the third flow sensor.

[0209] In this embodiment of the invention, a first flow sensor detects a first flow rate of the driving gas. A third flow sensor detects a third flow rate of the third gas delivered by the gas delivery branch.

[0210] In this embodiment of the invention, the first flow sensor can be installed in the intake branch. The first flow sensor can also be installed at the intersection of the intake branch and the exhaust branch. The third flow sensor is installed in the gas delivery branch.

[0211] S18, during the exhalation phase, expiratory gas is received from the patient interface, transmitted to the breathing container through the patient-end breathing system, and a fourth gas is received through the fresh gas interface, transmitted to the evaporator, and a fifth gas is carried out. The fifth gas is transmitted to the breathing container through the breathing gas branch, and excess mixed gas in the breathing container is discharged through the exhaust branch.

[0212] In this embodiment of the invention, during the exhalation phase, the patient exhales gas from the patient-end respiratory system and transfers it to the breathing container via the patient interface. Simultaneously, a fourth gas is received via the fresh gas interface and transferred to the evaporator. This fourth gas carries away a fifth gas from the evaporator and is then transferred to the breathing container via the patient-end respiratory system. The exhaled gas and the fifth gas compress excess mixed gas from the breathing container, and the excess mixed gas is discharged through the exhaust branch.

[0213] S19, the second flow rate of the mixed gas is detected by the second flow sensor, and the third flow rate of the fifth gas delivered by the gas delivery branch is detected by the third flow sensor.

[0214] In this embodiment of the invention, a second flow sensor detects the second flow rate of the mixed gas discharged from the exhaust branch. A third flow sensor detects the third flow rate of the fifth gas delivered by the gas delivery branch.

[0215] S20 calculates the tidal volume of one respiratory cycle based on the first flow rate, the second flow rate, and the third flow rate.

[0216] In this embodiment of the invention, during the inhalation phase, the processor adds the first flow rate to the third flow rate of the third gas to obtain the inspiratory tidal volume during the inhalation phase. During the exhalation phase, the processor subtracts the third flow rate of the fifth gas from the second flow rate to obtain the expiratory tidal volume during the exhalation phase. In this embodiment of the invention, the sum of the inspiratory tidal volume and the expiratory tidal volume equals the tidal volume of one respiratory cycle.

[0217] In some embodiments, see Figure 17 , Figure 17 This is a schematic diagram of an optional process for a respiratory ventilation method provided in an embodiment of the present invention. Figure 16 The shown S20 can be implemented through S21-S23, which will be explained in conjunction with each step.

[0218] S21 uses the first flow rate plus the third flow rate to obtain the inspiratory tidal volume.

[0219] In this embodiment of the invention, the processor adds the first flow rate to the third flow rate to obtain the inhaled tidal volume.

[0220] The first flow rate is the flow rate of the driving gas. The third flow rate is the flow rate of fresh gas during inhalation.

[0221] S22, the expiratory tidal volume is obtained by subtracting the third flow rate from the second flow rate.

[0222] In this embodiment of the invention, the processor subtracts the third flow rate of the fifth gas from the second flow rate to obtain the tidal volume of exhalation.

[0223] S23, add the inspiratory tidal volume and the respiratory tidal volume to obtain the tidal volume of one respiratory cycle.

[0224] In this embodiment of the invention, the processor adds the inspiratory tidal volume and the expiratory tidal volume to obtain the tidal volume of one cycle.

[0225] In this embodiment of the invention, a flow monitor is installed on one side of the machine-side breathing system, away from the patient. During the inhalation phase, a first gas in the breathing container is driven by a driving gas to the patient-side breathing system, which then transmits it to the patient interface. The flow monitor detects the first flow rate of the driving gas in the breathing container. Simultaneously, a third gas is transmitted through a gas transmission branch, and the third gas is transmitted to the patient interface through the patient-side breathing system. The third flow sensor detects the third flow rate of the third gas. During the exhalation phase, expiratory gas is received from the patient interface and transmitted to the breathing container via the patient-side respiratory system. Simultaneously, a fifth gas is received from the gas delivery branch and transmitted to the breathing container via the patient-side respiratory system. Under the action of the fifth gas and the expiratory gas, excess mixed gas in the breathing container is discharged through the exhaust branch. The second flow rate of the discharged mixed gas is detected by a flow monitor, and the fourth flow rate of the fifth gas delivered by the gas delivery branch is detected by a third flow sensor. The processor can calculate the tidal volume based on the first, second, and third flow rates. Since the flow monitor can monitor the gas flow rate in the machine-side respiratory system and takes into account the influence of different gas flow rates during inhalation and exhalation, the tidal volume obtained by this monitoring is highly accurate.

[0226] This invention provides an anesthesia machine, including a breathing and ventilation device with the above-described structure.

[0227] This invention also provides a computer-readable storage medium storing executable ventilation instructions, which, when executed by the processor of a respiratory ventilation device, implement the ventilation method provided in this invention.

[0228] In the embodiments of the present invention, the components can be integrated into one processing unit, or each unit can exist physically separately, or two or more units can be integrated into one unit. The integrated unit can be implemented in hardware or as a software functional module.

[0229] If the integrated unit is implemented as a software functional module and is not sold or used as an independent product, it can be stored in a computer-readable storage medium. Based on this understanding, the technical solution of this embodiment, in essence, or the part that contributes to the prior art, or all or part of the technical solution, can be embodied in the form of a software product. The computer software product is stored in a storage medium and includes several instructions to cause a computer device (which may be a personal computer, server, or network device, etc.) or processor to execute all or part of the steps of the method described in this embodiment. The aforementioned storage media include various media capable of storing program code, such as ferromagnetic random access memory (FRAM), read-only memory (ROM), programmable read-only memory (PROM), erasable programmable read-only memory (EPROM), electrically erasable programmable read-only memory (EEPROM), flash memory, magnetic surface memory, optical disc, or compact disc read-only memory (CD-ROM), etc., and the embodiments of the present invention are not limited thereto.

[0230] Industrial applicability

[0231] This invention provides a respiratory ventilation method, apparatus, anesthesia machine, and computer-readable storage medium. A flow monitor is installed on the machine-side respiratory system of the respiratory ventilation apparatus, located away from the patient end. During inhalation, a first gas in the breathing container is driven by a driving gas to the patient-side respiratory system, which then transmits it to the patient interface. The flow monitor detects the first flow rate of the driving gas in the breathing container. During exhalation, expiratory gas is received from the patient interface and transmitted to the breathing container via the patient-side respiratory system. Excess mixed gas in the breathing container is discharged through an exhaust branch, and the flow monitor detects the second flow rate of the mixed gas. The processor calculates the tidal volume for one respiratory cycle based on the first and second flow rates. Because the flow monitor can monitor gas flow in the machine-side respiratory system and takes into account the influence of different gas flow rates during inhalation and exhalation, the tidal volume obtained by this monitoring is highly accurate.

Claims

1. A breathing ventilation device, characterized in that, include: Patient-side respiratory system, machine-side respiratory system, flow monitor, and processor; The machine-based breathing system includes: an intake branch for the inhalation phase, a breathing container, and an exhaust branch for the exhalation phase. Both the intake branch and the exhaust branch are connected to the breathing container via the flow monitor, and the breathing container is connected to the patient-end breathing system. The breathing ventilation device further includes: a gas delivery branch, which is provided with a third flow sensor, a fresh gas interface and an evaporator; the evaporator is disposed between the fresh gas interface and the third flow sensor, and the end of the gas delivery branch near the third flow sensor is connected between the breathing container and the patient interface; The processor is connected to the flow monitor; The flow monitor is located on one side of the machine-side respiratory system, away from the patient-side respiratory system. During the inhalation phase, the flow monitor is used to detect the first flow rate of the driving gas in the breathing container; the driving gas is used to drive the first gas in the breathing container to the patient-end breathing system; the fresh gas interface receives the second gas, transmits the second gas to the evaporator, carries out the third gas, transmits the third gas to the patient interface via the patient-end breathing system; and the third flow rate of the third gas delivered by the gas delivery branch is detected by the third flow sensor. During the exhalation phase, the flow monitor is used to detect a second flow rate of the mixed gas in the breathing container, the mixed gas being a mixture of driving gas, anesthetic gas, and expiratory gas; the fresh gas interface receives a fourth gas, transmits the fourth gas to the vaporizer, carries out a fifth gas, transmits the fifth gas to the breathing container via the patient-end respiratory system; and the third flow rate of the fifth gas delivered by the gas delivery branch is detected by the third flow sensor. The processor is capable of calculating the inspiratory tidal volume during the inhalation phase using the first flow rate and the third flow rate of the third gas; and / or the processor is capable of calculating the expiratory tidal volume during the exhalation phase using the second flow rate and the third flow rate of the fifth gas.

2. The breathing ventilation device according to claim 1, characterized in that, The flow monitor is a bidirectional flow sensor.

3. The breathing ventilation device according to claim 1, characterized in that, The flow monitor is a unidirectional flow sensor; the flow monitor includes: a first flow sensor and a second flow sensor; The first flow sensor is connected to the intake branch, and the second flow sensor is connected to the exhaust branch.

4. The breathing ventilation device according to claim 1, characterized in that, The breathing ventilation device further includes: a first one-way valve and a second one-way valve; the flow monitor is a one-way flow sensor; the flow monitor includes: a first flow sensor and a second flow sensor; The first one-way valve is used to transfer the driving gas in the intake branch to the breathing container; The second one-way valve is used to transfer the mixed gas in the breathing container to the exhaust branch; The intake branch is connected to the breathing container via the first flow sensor and the first one-way valve; the exhaust branch is connected to the breathing container via the second flow sensor and the second one-way valve; the first one-way valve is connected to the first flow sensor, and the second one-way valve is connected to the second flow sensor.

5. The breathing ventilation device according to claim 1, characterized in that, The patient-side respiratory system also includes: an inspiratory branch and an expiratory branch; Both the inspiratory branch and the expiratory branch are connected to the breathing container at one end of the common connection between the inspiratory branch and the expiratory branch. The gas delivery branch is connected to the inspiratory branch, and the patient interface is located at the other end of the common connection between the inspiratory branch and the expiratory branch.

6. The breathing ventilation device according to claim 1, characterized in that, The breathing apparatus includes: an air mask, an air bag, and an air valve; The airbag is disposed inside the air mask cavity and is connected to the patient's respiratory system. The airbag has a deformable structure, and the gas inside and outside the airbag is isolated. The end of the gas delivery branch near the third flow sensor is connected between the airbag and the patient interface. The air intake branch is connected to the air cover but not to the airbag, and the exhaust branch is connected to the airbag through the air valve.

7. The breathing ventilation device according to claim 1, characterized in that, The breathing container includes: an exchange chamber; The exchange chamber is a hollow tubular structure. One end of the exchange chamber is connected to the air intake branch and the air exhaust branch, and the other end of the exchange chamber is connected to the patient-side breathing system. The end of the gas delivery branch near the third flow sensor is connected between the other end of the exchange chamber and the patient interface.

8. The breathing ventilation device according to claim 2, characterized in that, The flow monitor is located at the intersection of the intake branch and the exhaust branch.

9. A storage medium storing executable instructions configured to cause a processor to execute the executable instructions to implement a breathing ventilation method, characterized in that, The method is applied in a respiratory ventilation device, which includes a patient-end respiratory system, a machine-end respiratory system, a flow monitor, and a processor. The machine-end respiratory system includes an intake branch for inhalation, a breathing container, and an exhaust branch for exhalation. Both the intake branch and the exhaust branch are connected to the breathing container via the flow monitor, and the breathing container is connected to the patient-end respiratory system. The respiratory ventilation device further includes a gas delivery branch, which is equipped with a third flow sensor, a fresh gas interface, and an evaporator. The evaporator is located between the fresh gas interface and the third flow sensor, and the end of the gas delivery branch near the third flow sensor is connected between the breathing container and the patient interface. The processor is connected to the flow monitor. The flow monitor is located on one side of the machine-end respiratory system, away from the patient-end respiratory system. The method includes: During the inhalation phase, the flow monitor detects the first flow rate of the driving gas in the breathing container; the driving gas is used to drive the first gas in the breathing container to the patient-end breathing system; the fresh gas interface receives the second gas, transmits the second gas to the evaporator, carries out the third gas, transmits the third gas to the patient interface via the patient-end breathing system; and the third flow rate of the third gas delivered by the gas delivery branch is detected by the third flow sensor. During the exhalation phase, the flow monitor monitors the second flow rate of the mixed gas in the breathing container, which is a mixture of driving gas, anesthetic gas, and expiratory gas; the fresh gas interface receives a fourth gas, transmits the fourth gas to the vaporizer, carries out a fifth gas, and transmits the fifth gas to the breathing container via the patient-end respiratory system; and the third flow sensor detects the third flow rate of the fifth gas delivered by the gas delivery branch. The inspiratory tidal volume during the inhalation phase is calculated based on the first flow rate and the third flow rate of the third gas; and / or the expiratory tidal volume during the exhalation phase is calculated based on the second flow rate and the third flow rate of the fifth gas.

10. The storage medium according to claim 9, characterized in that, The flow monitor includes: a first flow sensor and a second flow sensor; The step of detecting the first flow rate of the driving gas in the breathing container by the flow monitor includes: The first flow rate of the driving gas in the breathing container is detected by the first flow sensor; The second flow rate of the mixed gas in the breathing container detected by the flow monitor includes: The second flow rate of the mixed gas in the breathing container is detected by the second flow sensor.

11. The storage medium according to claim 9, characterized in that, The third flow rate of the fifth gas delivered by the gas delivery branch is detected by the third flow sensor, including: At the end of expiration, the third flow rate monitored by the third flow sensor is taken as the third flow rate of the fifth gas; or, The third flow rate of the fifth gas is determined based on the third flow rate detected by the third flow sensor and the functional relationship between the driving gas flow rate and the fresh gas flow rate.

12. The storage medium according to claim 9, characterized in that, The step of calculating the inhalation tidal volume during the inhalation phase based on the first flow rate and the third flow rate of the third gas includes: adding the first flow rate to the third flow rate to obtain the inhalation tidal volume; Calculating the expiratory tidal volume during the exhalation phase based on the second flow rate and the third flow rate of the fifth gas includes: subtracting the third flow rate from the second flow rate to obtain the expiratory tidal volume.

13. An anesthesia machine, characterized in that, include: The breathing ventilation device as described in any one of claims 1-8.

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