CN115607781A

CN115607781A - Breathing machine

Info

Publication number: CN115607781A
Application number: CN202110420665.8A
Authority: CN
Inventors: 请求不公布姓名
Original assignee: Shenzhen Minghua Electromechanical Co ltd
Current assignee: Shenzhen Minghua Electromechanical Co ltd
Priority date: 2021-04-20
Filing date: 2021-04-20
Publication date: 2023-01-17

Abstract

The present application provides a ventilator. The breathing gas circuit module of the breathing machine comprises a fan and a one-way valve which are sequentially arranged along the breathing direction, and the breathing gas circuit module comprises a breathing valve and a breathing valve driving device. The control module generates a control instruction according to signals of the sensors in the air circuit module, and regulates and controls the rotating speed of the blower and/or the acting force of the expiratory valve driving device on the expiratory valve diaphragm in real time through the control instruction, so that the work of the respirator is controlled. When the gas pressure at the patient end is lower than the target pressure, the control module generates a first control instruction, and increases the rotating speed of the fan and/or increases the acting force of the expiratory valve driving device on the diaphragm of the expiratory valve through the first control instruction so as to increase the gas pressure at the patient end; when the gas pressure at the patient end is higher than the target pressure, the control module generates a second control instruction, and reduces the acting force of the expiratory valve driving device on the diaphragm of the expiratory valve and/or reduces the rotating speed of the fan through the second control instruction so as to reduce the gas pressure at the patient end.

Description

Breathing machine

Technical Field

The present application relates to the field of breathing apparatus, in particular to ventilators.

Background

According to the power supply classification, the breathing machine mainly divides into pneumatic breathing machine and electronic breathing machine, because pneumatic breathing machine simple structure, easily control, and can acquire less tidal volume, consequently the application is comparatively general. But because it requires an additional air source and is bulky, it is generally suitable for patients who are on machines for a long time, and is inconvenient for transferring among wards.

Disclosure of Invention

In order to solve the technical problem, the application provides a breathing machine. The breathing machine comprises: a gas circuit module comprising an inhalation gas circuit module and an exhalation gas circuit module, wherein the inhalation gas circuit module comprises a blower and a one-way valve configured to allow one-way flow of gas in a direction toward a patient, wherein the one-way valve is downstream of the blower, and the exhalation gas circuit module comprises an exhalation valve and an exhalation valve driving device; and the control module is connected with the pressure sensor and the flow sensor, receives measurement signals from the pressure sensor and the flow sensor when in work, generates a control command according to the measurement signals, and regulates and controls the rotating speed of the fan and/or the acting force of the exhalation valve driving device on the exhalation valve diaphragm through the control command so as to control the work of the respirator, wherein when the gas pressure at the patient end is less than the target pressure, the control module generates a first control command, and increases the rotating speed of the fan and/or increases the acting force of the exhalation valve driving device on the exhalation valve diaphragm through the first control command so as to increase the gas pressure at the patient end, and when the gas pressure at the patient end is greater than the target pressure, the control module generates a second control command, and decreases the acting force of the exhalation valve driving device on the exhalation valve diaphragm and/or decreases the rotating speed of the fan through the second control command so as to decrease the gas pressure at the patient end.

In some embodiments, when the patient end gas pressure is greater than the target pressure and there is an inspiratory flow rate in the inspiratory gas circuit, the control module decreases the patient end gas pressure by at least one of: controlling to reduce the rotating speed of the fan to reduce the air supply flow rate in the air suction path, and controlling to reduce the acting force of the exhalation valve driving device on the exhalation valve membrane to increase the air discharge flow rate in the exhalation air path; when the gas pressure at the patient end is higher than the target pressure and the gas supply flow rate is not available in the inspiration gas circuit, the control module controls to reduce the acting force of the expiration valve driving device on the expiration valve membrane so as to increase the gas discharge flow rate in the expiration gas circuit, so that the gas pressure at the patient end is reduced; when the patient end gas pressure is less than the target pressure and there is a flow rate of exhaust gas in the expiratory gas circuit, the control module increases the patient end gas pressure by at least one of: controlling and increasing the rotating speed of the fan to increase the air supply flow rate in the air suction path, and controlling and increasing the acting force of the exhalation valve driving device on the exhalation valve membrane to reduce the air discharge flow rate in the exhalation air path; when the gas pressure at the patient end is lower than the target pressure and the air discharge flow rate in the expiration air circuit is not high, the control module controls the fan to increase the air discharge flow rate in the inspiration air circuit, so that the gas pressure at the patient end is increased.

In some embodiments, wherein: the inspiratory circuit module comprises an air circuit, an oxygen circuit and a mixing circuit, wherein the air circuit comprises an air flow passage, the air flow passage is communicated with an air inlet and a mixing chamber, the air flow passage is configured to guide air from the air inlet to the mixing chamber, the oxygen circuit comprises an oxygen flow passage, the oxygen flow passage is communicated with the oxygen inlet and the mixing chamber, the oxygen flow passage is configured to guide oxygen from the oxygen inlet to the mixing chamber, the air and the oxygen are mixed into mixed gas in the mixing chamber, the mixing circuit comprises a mixed gas flow passage, the mixed gas flow passage is communicated with the mixing chamber and a patient interface, the mixed gas flow passage is configured to guide the mixed gas from the mixing chamber to the patient interface, and the blower and the one-way valve are both arranged in the mixing circuit; the at least one pressure sensor comprises a first pressure sensor, wherein the first pressure sensor is connected to the inspiratory gas path downstream of the blower and upstream of the one-way valve, the first pressure sensor configured to measure a gas pressure within the inspiratory gas path downstream of the blower and upstream of the one-way valve; and the patient-side gas pressure is obtained by the control module based on measurement data of a second pressure sensor, wherein: the second pressure sensor is connected to an inspiratory air path downstream of the one-way valve, the second pressure sensor is connected to an expiratory air path, and/or the second pressure sensor is connected to a patient-side air path.

In some embodiments, wherein the oxygen inlet comprises a hyperbaric oxygen inlet, the inspiratory gas circuit module further comprises a hyperbaric oxygen regulation device connected in the oxygen gas circuit downstream of the hyperbaric oxygen inlet and upstream of the mixing chamber, wherein the hyperbaric oxygen regulation device comprises: the pressure regulating device comprises a pressure regulating valve and a first supporting drainage piece, wherein the first supporting drainage piece comprises a first chamber, a first flow passage and a second flow passage, the first flow passage and the second flow passage are communicated with the first chamber, the first end of the pressure regulating valve is installed in the first chamber, the end face of the first end is spaced from the bottom of the first chamber by a preset distance, so that a drainage cavity is formed between the first end and the side wall of the first chamber, the air inlet of the pressure regulating valve is communicated with the drainage cavity, the first flow passage is communicated with the drainage cavity, the first supporting drainage piece conducts air to the air inlet of the pressure regulating valve through the first flow passage and the drainage cavity, the second flow passage corresponds to and is communicated with the air outlet of the pressure regulating valve, and the first supporting drainage piece conducts the air flowing out of the air outlet of the pressure regulating valve to an air passage at the downstream of the pressure regulating assembly through the second flow passage; and/or flow control device, support the drainage piece including flow control valve and second, wherein, the second supports the drainage piece and includes that first connection chamber and second connect the chamber, the entry of first connection chamber is the high-pressure gas entry, the lateral wall that the chamber was connected to the second is provided with the low-pressure gas entry, flow control valve installs on the second supports the drainage piece, flow control valve's air inlet with the export intercommunication in first connection chamber, flow control valve's gas outlet with the entry intercommunication in chamber is connected to the second.

In some embodiments, the air suction path module further includes a silencing and mixing device, the silencing and mixing device includes a first channel, a second channel, and a mixing cavity, the first channel and the second channel are communicated with the mixing cavity, the first channel forms at least a portion of the air path, the second channel forms at least a portion of the oxygen path, the mixing cavity forms the mixing chamber, the mixing cavity includes a mixing cavity outlet, the mixing cavity outlet is communicated with the air inlet of the fan, wherein the silencing and mixing device includes a silencing box and a plurality of silencing pieces, the plurality of silencing pieces are disposed in the silencing box, so that the silencing and mixing device forms the first channel and the mixing cavity, and the plurality of silencing pieces are made of silencing materials and configured to eliminate noise of the air entering the fan through the silencing and mixing device.

In some embodiments, wherein, the air intake circuit module further includes a filtering device, the filtering device is connected in the air circuit of air inlet downstream and noise reduction box upstream, wherein the filtering device includes an installation shell, a primary filter cotton, a high-efficiency filter cotton and a sealing gasket, the installation shell includes an installation shell inlet, an installation shell outlet and a communication installation cavity of the installation shell inlet and the installation shell outlet, the primary filter cotton and the high-efficiency filter cotton are arranged in the installation shell and configured to filter the air passing through the filtering device, the sealing gasket is arranged at one end of the installation shell outlet, a buckle is designed on the installation shell, wherein the noise reduction box further includes a filtering device accommodating cavity configured to accommodate the filtering device, a wall plate of the filtering device accommodating cavity is provided with a clamping groove configured to allow the buckle of the installation shell to be clamped, so that the filtering device is fixed in the filtering device accommodating cavity.

In some embodiments, the air suction path module further includes a damping component, the damping component includes a damping box and a damping member, the damping box has a cavity structure, the blower is at least partially inside the damping box, the damping member is filled in a space between the blower and an inner wall of the damping box to reduce vibration of the blower during operation, the damping box includes a first opening and a second opening, the first opening corresponds to an air inlet of the blower and is communicated with the air inlet of the blower so as to guide the mixed gas from the first opening to the air inlet of the blower, and the second opening corresponds to an air outlet of the blower and is configured to allow an air outlet connecting pipe connected to the air outlet of the blower to pass through so as to guide the mixed gas flowing out of the air outlet to an air path downstream of the blower.

In some embodiments, wherein the shock assembly further comprises: the air inlet connecting pipe is connected with one end of the air inlet connecting pipe and the air inlet connecting part of the shock absorption box, and the other end of the air inlet connecting pipe is connected with the air inlet of the fan, so that the air inlet connecting part of the shock absorption box is communicated with the air inlet of the fan; and/or the air outlet adapter tube, one end with the air outlet of fan is connected, wherein the air outlet adapter tube is located the part outside the shock attenuation box is provided with first detection interface, at least one pressure sensor is including being connected to the first pressure sensor of the third gas pipeline of fan low reaches and patient interface upper reaches, first pressure sensor with first detection interface connection, and through first detection interface connection to the third gas pipeline.

In some embodiments, the inspiration gas circuit module further includes an oxygen concentration sensor connected to the inspiration gas circuit downstream of the one-way valve, the oxygen concentration sensor being configured to measure the oxygen concentration in the gas in the inspiration gas circuit, wherein the inspiration gas circuit module further includes an inspiration gas circuit outlet connector having a gas flow channel, a side wall of the gas flow channel being provided with a second detection interface, and the oxygen concentration sensor being connected to the second detection interface and connected to the inspiration gas circuit through the second detection interface.

In some embodiments, wherein the gas circuit module further comprises: a safety valve connected to an inspiratory gas circuit downstream of the one-way valve, the safety valve configured to provide a breathing pathway to a patient to prevent a patient from an apneic event when the ventilator is powered down or fails; the inspiration keeping valve is connected in the inspiration gas path, and is configured to cut off the inspiration branch when the patient needs inspiration keeping, so that the pressure in the airway of the patient is kept at a preset value within a certain time without attenuation; the zero calibration valve is connected with the target pressure sensor and is configured to perform timing zero calibration on the target pressure sensor, so that the phenomenon that the error of measured data is overlarge due to zero drift of the target pressure sensor is avoided; a blood oxygen test connector configured to allow access of a blood oxygen test device to monitor blood oxygen content of a patient; CO2 ₂ A test joint configured to allow CO ₂ The test device is switched on to thereby detect CO in the gas exhaled by the patient ₂ Monitoring the content; and/or a purge module operative to impart a purge flow to the sensor sampling tube to prevent the contamination source from clogging the sensor sampling tube or contaminating the sensor through the sensor sampling tube.

The application provides a ventilator: on one hand, the air supply flow rate is adjusted by adjusting the rotating speed of the fan, the air release flow rate is adjusted by adjusting the driving force of the expiratory valve driving device on the diaphragm of the expiratory valve, the adjustment of the flow rate of a patient end and the pressure of the patient end is realized, an additional air source is not required, an air compressor is omitted, the problem that the pneumatic respirator needs the heavy air source is solved, an additional flow control device (such as a proportional valve) is not required, the control system is simplified, and the cost is reduced; on the other hand, compare in the condition that combines flow control device to control patient end gas pressure through the hierarchical rotational speed of control fan and increase and reduce, the breathing machine that this application provided, control module regulates and control fan rotational speed and/or driving motor to the effort of expiratory valve in real time according to the measuring signal of sensor, fan rotational speed and driving motor all can be along with patient end pressure measured value real-time change to the effort of expiratory valve, do not need additionally to add flow control device in the mixed gas circuit of inhaling the module, the structure of inhaling the gas circuit is simpler, the breathing machine overall control scheme is also simpler, and the breathing machine wholly has higher response speed. Furthermore, a safety valve in the respirator can perform overvoltage protection and power-down protection on a patient; the inspiration keeping valve can realize inspiration keeping, and can ensure that certain patients in need can complete sufficient oxygenation process in an inspiration stage; the mouth end flow sensor (namely the second flow sensor 811) can more accurately detect the tidal volume of the patient and feed the tidal volume back to the breathing machine control module in real time, so that the human-computer synchronization effect is better; the purging component can effectively prevent water drops in the sampling pipe of the mouth end flow sensor from being condensed to influence the measurement precision; high-pressure gas adjusting part can carry out steady voltage and current-limiting to high-pressure oxygen source, simultaneously, still is provided with the low-pressure oxygen source interface on the high-pressure gas adjusting part, when hospital's oxygen source pressure is not enough or does not have the high-pressure oxygen source, can let in low-pressure oxygen at the low-pressure oxygen source interface and continue to treat the patient, still includes the atomizing runner among the high-pressure gas adjusting part, and the atomizing runner can provide atomizing oxygen source for the patient that needs medication.

Drawings

Fig. 1A illustrates a schematic diagram of an airway structure of a ventilator provided in accordance with an embodiment of the present application;

FIG. 1B is a schematic diagram illustrating a gas circuit structure of a ventilator including a purge module according to an embodiment of the present disclosure;

FIG. 2A illustrates a pressure-time curve during operation of a ventilator provided in accordance with an embodiment of the present application;

FIG. 2B is a graph illustrating a relationship between a target value and an actual measured value of a pressure-time curve of a ventilator according to an embodiment of the present disclosure;

fig. 3 is a schematic diagram illustrating a hardware structure of a ventilator according to an embodiment of the present application;

FIG. 4A is a schematic diagram illustrating the connection of a filter assembly, a silencing and mixing device, a shock absorbing assembly and a fan according to an embodiment of the present application;

FIG. 4B illustrates a partial cross-sectional view of a sound attenuating mixing device and shock absorbing assembly according to an embodiment of the present application;

FIG. 4C illustrates a partial cross-sectional view of a damper assembly and a fan provided in accordance with an embodiment of the present application;

FIG. 4D illustrates an isometric view of a sound damping cassette provided in accordance with an embodiment of the present application;

FIG. 4E illustrates an isometric view of another orientation of a sound damping cassette provided in accordance with an embodiment of the present application;

FIG. 4F illustrates a schematic structural diagram of a filter assembly provided in accordance with an embodiment of the present application;

FIG. 5A shows a schematic structural diagram of a high pressure gas regulating device provided in accordance with the present application;

FIG. 5B illustrates a schematic structural diagram of a pressure adjustment assembly provided in accordance with an embodiment of the present application;

FIG. 5C illustrates a partial cross-sectional view of a pressure adjustment assembly provided in accordance with an embodiment of the present application;

FIG. 5D illustrates a partial cross-sectional view of a first support drain provided in accordance with an embodiment of the present application;

FIG. 5E illustrates a partial cross-sectional view of a pressure adjustment assembly provided in accordance with an embodiment of the present application;

FIG. 5F is a schematic diagram illustrating a flow regulating assembly according to an embodiment of the present application;

FIG. 5G illustrates a partial cross-sectional view of a second support drain provided in accordance with an embodiment of the present application;

FIG. 6A illustrates a schematic structural diagram of a suction holding valve provided in accordance with an embodiment of the present application;

fig. 6B shows a schematic diagram of an operation principle of a safety valve provided according to an embodiment of the present application.

Detailed Description

The following description is presented to enable one of ordinary skill in the art to make and use the present disclosure. These and other features of the present disclosure, as well as the operation and function of the related elements of the structure, and the combination of parts and economies of manufacture, may be particularly improved upon in view of the following description. All of which form a part of this disclosure, with reference to the accompanying drawings. It is to be expressly understood, however, that the drawings are for the purpose of illustration and description only and are not intended as a definition of the limits of the disclosure. Various local modifications to the disclosed embodiments will be readily apparent to those skilled in the art, and the general principles defined herein may be applied to other embodiments and applications without departing from the spirit and scope of the present disclosure. Thus, the present disclosure is not to be limited to the embodiments shown, but is to be accorded the widest scope consistent with the claims.

The present application provides a ventilator. As an example, fig. 1A illustrates a schematic diagram of an air circuit structure of a ventilator 001 according to an embodiment of the present application. Specifically, ventilator 001 may include an inhalation module 002, an exhalation module 003, and a control module 004.

The inhalation module 002 comprises an inhalation air path. The air suction circuit may include an air circuit L1, an oxygen circuit L2, and a mixture circuit L3.

The air path L1 includes an air flow passage communicating with an air inlet and the mixing chamber 803, and the air flow passage is configured to guide air from the air inlet to the mixing chamber 803.

The oxygen gas path L2 includes an oxygen gas flow path communicating an oxygen gas inlet and the mixing chamber 803, the oxygen gas flow path is configured to guide oxygen gas from the oxygen gas inlet to the mixing chamber 803, and the air and the oxygen gas are mixed into a mixed gas in the mixing chamber 803. As an example, the oxygen inlet may be in communication with an outlet of an oxygen source. By way of example, the oxygen source may be a high pressure oxygen source or a low pressure oxygen source.

The mixed gas path L3 includes a mixed gas flow path, which communicates the mixing chamber 803 with a suction gas path outlet, and is configured to guide the mixed gas from the mixing chamber 803 to the suction gas path outlet.

Specifically, the air path L1 may include a filtering unit 801 and/or a silencing unit 802. In the suction direction, the filter unit 801 may be disposed upstream of the muffler unit 802. Specifically, the oxygen gas circuit L2 may include an oxygen source 814, a high pressure gas regulator 815, and/or an oxygen flow sensor 816. The oxygen source 814, the high pressure gas regulator 815 and the oxygen flow sensor 816 are provided in this order in the inhalation direction. Specifically, the mixed gas path L3 may include a blower 804, a first pressure sensor 805, a first flow sensor 806, a check valve 807, an inspiratory hold valve 808, a safety valve 809, and/or an oxygen concentration testing device 810. In the air suction direction, the first pressure sensor 805 and the first flow sensor 806 are disposed downstream of the fan 804, the first pressure sensor 805 is configured to measure the pressure of the mixed gas output by the fan 804, and the first flow sensor 806 is configured to measure the flow rate of the mixed gas output by the fan 804.

The oxygen concentration sensor 810 is disposed in the inhalation gas path. Specifically, the oxygen concentration sensor 810 is provided in the mixed gas path L3. In the inspiration direction, the oxygen concentration sensor 810 is disposed downstream of the one-way valve 807 and near the patient end. The oxygen concentration sensor 810 is configured to measure the oxygen concentration in the inspiratory gas path. The air suction circuit module further comprises an air suction circuit outlet connecting piece, the air suction circuit outlet connecting piece is provided with an air flow channel, the side wall of the air flow channel is provided with a first detection interface, and the oxygen concentration sensor is connected with the second detection interface and is connected to the air suction circuit through the second detection interface. As an example, the inspiratory gas path outlet connection may be an inspiratory valve.

A check valve 807 is disposed downstream of the fan 804 in the suction direction. The one-way valve 807 is configured to allow one-way flow of gas output by the fan 804 in the suction direction. The inspiratory air circuit further comprises an inspiratory hold valve 808 and/or a safety valve 809. The relief valve 809 and the suction maintaining valve 808 are disposed downstream of the first flow sensor 806 and upstream of the oxygen concentration sensor 810. The check valve 807 may be disposed downstream of the first flow sensor 806, the inhalation hold valve 808 may be disposed downstream of the check valve 807, and the safety valve 809 may be disposed downstream of the inhalation hold valve 808 and upstream of the oxygen concentration test apparatus 801. It should be noted that in some embodiments, the oxygen concentration testing device, the first pressure sensor, the first flow sensor, the inspiratory hold valve, and/or the safety valve may also be disposed at other locations in the mixed gas path without affecting the core spirit of the present application.

In some embodiments, a purge module is also included in ventilator 001. When the respirator 001 works, the purging module can provide continuous purging airflow for the patient-end flow sensor, so that inaccurate flow test caused by blocking of a pressure sampling pipe of the flow sensor by water vapor or pollutants in a breathing pipeline is prevented. By way of example, fig. 1B illustrates a schematic diagram of a gas circuit structure of a ventilator 001 including a purge module according to an embodiment of the present application. The purge module 005 may include a purge gas line L6. Purge circuit L6 may be connected at one end downstream of one-way valve 807 and at the other end to patient end flow sensor 811. In some embodiments, at least one pressure sampling port may be disposed in the purge gas line L6, and a patient end pressure sensor 817 may be connected to the pressure sampling port to measure the patient end gas pressure.

The exhalation module 003 includes an exhalation air passage L4. The expiratory air passage L4 includes an expiratory valve 813 and a drive motor 812. As an example, the exhalation valve 813 has one end in air passage communication with the patient end and the other end in communication with the atmosphere. The drive motor 812 may control the actuation of the diaphragm of the exhalation valve 813, thereby controlling the opening or closing of the valve body passages in the exhalation valve 813. When the valve body passage of the exhalation valve 813 is opened, the gas in the patient end air passage can be exhausted to the atmosphere through the exhalation air passage L4 and via the valve body passage of the exhalation valve 813. It should be noted that the structure of the exhalation valve in the exhalation circuit shown in fig. 1A is only described as an example for the force applied to the diaphragm, and the exhalation valve may have other structures without affecting the core spirit of the present application.

In some embodiments, ventilator 001 may also include a patient end airway L5. One end of the patient end air passage L5 can be communicated with a target part of a patient. By way of example, the target site may include a respiratory organ of a patient, including, but not limited to, a lung, a trachea, a mouth, etc., of the patient. The other end of the patient end air passage L5 is communicated with the outlet of the inspiration air passage and the inlet of the expiration air passage. The outlet of the inspiration circuit may be an outlet of the inspiration circuit (e.g., at K1 in fig. 1A) that outputs gas during inspiration, and the inlet of the expiration circuit may be an inlet of the expiration circuit (e.g., at K2 in fig. 1A) into which gas expired by the patient during expiration.

In some embodiments, a patient end flow sensor 811 is disposed in patient end airway L5. A patient end flow sensor 811 is disposed near one end of the patient. The patient end flow sensor 811 is configured to measure the gas flow rate/flow in the patient end airway.

As described above, a first pressure sensor 805 is connected to the inhalation air path, and the first pressure sensor 805 is disposed downstream of the blower 804 and upstream of the check valve 807 in the inhalation direction and configured to measure the pressure of the gas in the flow path between the blower 804 and the check valve 807.

In some embodiments, a second pressure sensor 817 is also included in the ventilator 001, and the second pressure sensor 817 can be used to measure the pressure of the patient end gases. The pressure of the gas at the patient end refers to the pressure of the gas in the line near the patient. For convenience of description, the second pressure sensor is referred to as a "patient end pressure sensor" in the following description of the present application. In some embodiments, the patient end gas pressure is obtained by the control module based on measurement data of a second pressure sensor. The patient side gas pressure may be obtained directly by the control module based on the measurement data of the second pressure sensor, or the patient side gas pressure may be obtained indirectly by the control module based on the measurement data of the second pressure sensor.

In some embodiments, a patient end pressure sensor 817 may be disposed in the inspiratory air passage, and in the inspiratory direction, the patient end pressure sensor 817 is connected to the air passage downstream of the one-way valve 807. In some embodiments, a patient end pressure sensor 817 may be disposed in the expiratory airway. In some embodiments, a patient end pressure sensor 817 may be disposed in the patient end airway. Referring to fig. 1A, due to the one-way shutoff of the one-way valve 807, the gas pressure in the gas path segment of the mixing gas path downstream of the one-way valve 807, the expiratory gas path, and the patient side gas path are the same. Therefore, the patient end pressure sensor 817 is arranged in the three air paths to measure the gas pressure at the patient end. For ease of description, the present application is described in the following description with the patient end pressure sensor 817 disposed in the patient end airway.

With continued reference to fig. 1A, the control module 004 interfaces with various pressure and flow sensors in the ventilator 001. By way of example, the pressure sensor and flow sensor may include, but are not limited to, an oxygen flow sensor 816 disposed in the oxygen line L2 for measuring the flow of oxygen, a first flow sensor 806 disposed in the mixed gas line L3 for measuring the flow of the mixed gas, a first pressure sensor 805 disposed in the mixed gas line L3 for measuring the pressure of the mixed gas, a patient end pressure sensor 817 disposed at the patient end for measuring the pressure at the patient end, and a patient end flow sensor 811 disposed at the patient end for measuring the flow at the patient end.

The control module 004 can receive the measurement signals from the pressure sensors and the flow sensors, generate various control commands according to the measurement signals, and control the actions of the high-pressure gas regulating device 815, the fan 804, the suction holding valve 808, the safety valve 809 and/or the driving motor 812 through the control commands. After the high-pressure gas adjusting device 815, the fan 804, the suction holding valve 808, the safety valve 809 and/or the driving motor 812 act, the flow, pressure and/or concentration at different parts in the gas path are fed back to the control module 004 through various sensors, so that closed-loop control is realized.

As an example, the control module 004 may receive the measurement signals from the sensors, generate a control command according to the measurement signals, and regulate the rotation speed of the blower 804 and/or the acting force of the output component of the driving motor 812 on the diaphragm of the exhalation valve 813 through the control command, so as to control the operation of the ventilator 001.

In some embodiments, the adjustment of the rotational speed of the fan 804 by the control module 004 may be in real time, dynamically, and/or continuously. The real-time, dynamic and/or continuous reference to the fan different from the fixed rotation speed (i.e. the rotation speed of the fan only includes a specific number of stages), the adjustment of the rotation speed of the fan by the control module in the present application is not limited to a specific number of stages, and the control module can adjust the rotation speed of the fan to any one rotation speed value according to the measurement signal of the sensor. The rotation speed of the fan is dynamically changed along with the measuring signal and is not limited to a specific rotation speed level.

In some embodiments, the control module 004 can control the operation of the ventilator by controlling the gas pressure at the patient end only by regulating the rotational speed of the blower 804 and/or the force of the output component of the drive motor 812 on the diaphragm of the exhalation valve 813 without the need for additional flow control devices (e.g., proportional valves).

Patient end pressure and patient end flow rate are correlated. As an example, the patient-side pressure is substantially proportional to the integral of the patient-side flow rate (inspiratory limb-expiratory limb). Thus, the regulatory objective may also be described in terms of flow rate without affecting the core spirit of the present application. It should be noted that, in the description of the present application, the magnitude of the flow rate in the gas circuit refers to the magnitude of the absolute value of the flow rate in the gas circuit.

For ease of description, in the following description of the present application, the flow rate of the inspiratory flow delivered by the inspiratory limb to the patient end is referred to as "inspiratory flow rate", and the flow rate of the expiratory flow discharged (to atmosphere) by the expiratory limb is referred to as "expiratory flow rate". In the description of the present application, "having" a flow rate of supply air may mean that the flow rate of supply air in the inspiration branch is greater than 0, "not having" a flow rate of supply air may mean that the flow rate of supply air in the inspiration branch is equal to 0, "having" a flow rate of discharge air may mean that the flow rate of discharge air in the expiration branch is greater than 0, and "not" a flow rate of discharge air may mean that the flow rate of discharge air in the expiration branch is equal to 0. It should be noted that, in the foregoing description, with "0" as the boundary for distinguishing "flow rate" and "no flow rate" in the inspiration branch and the expiration branch, in the actual operation of the ventilator, a threshold may also be set as the boundary for "flow rate" and "no flow rate", without affecting the core spirit of the present application. As an example, the threshold may be a value close to 0. An increase in the bleed air flow rate and/or a decrease in the bleed air flow rate will result in an increase in patient end flow rate and an increase in patient end pressure. A decrease in the inflow rate and/or an increase in the outflow rate will result in a decrease in patient end flow rate and a decrease in patient end pressure.

As an example, the control module 004 can regulate the flow rate of the supplied air only by regulating the rotation speed of the fan 804, and does not need to regulate other flow control devices (such as a proportional valve). For example, the control module 004 may increase the rotational speed of the fan to increase the flow rate of the supplied air, and the control module may decrease the rotational speed of the fan to decrease the flow rate of the supplied air. As an example, the control module 004 may implement the regulation of the bleed flow rate by regulating the driving force of the exhalation valve driving device on the exhalation valve diaphragm only. For example, the control module may decrease the driving force of the exhalation valve driving device on the exhalation valve diaphragm to increase the exhalation flow rate, and the control module may increase the driving force of the exhalation valve driving device on the exhalation valve diaphragm to decrease the exhalation flow rate.

In the working process of the breathing machine, when the gas pressure at the patient end is smaller than the target pressure and the gas pressure at the patient end needs to be increased, the control module generates a first control instruction, and increases the rotating speed of the fan (increasing the air supply flow rate of the inspiration branch) and/or the acting force of the expiration valve driving device on the diaphragm of the expiration valve (reducing the air discharge flow rate of the expiration branch and ensuring that the air discharge flow rate of the minimum expiration branch is 0) through the first control instruction, so that the pressure at the patient end is increased.

As an example, when the patient end pressure is less than the target pressure, and there is a bleed flow rate (bleed flow rate greater than 0), increasing the turbine speed either increases the bleed flow rate or decreases the bleed flow rate to assist in the patient end pressure increase. At this time: the control module can maintain the state of the expiratory valve and only increase the rotating speed of the turbine to improve the flow rate of the delivered air so as to increase the pressure at the patient end; the control module may also maintain the turbine state, only reducing the bleed flow rate, thereby increasing the patient end pressure; the control module may also simultaneously increase the patient side pressure and decrease the exhaust flow rate, thereby increasing the patient side pressure.

As an example, when the patient-side pressure is less than the target pressure and there is no bleed flow rate (bleed flow rate is 0), the control module can only increase the patient-side pressure by increasing the bleed flow rate by increasing the speed of the turbine.

In the working process of the breathing machine, when the gas pressure at the patient end is larger than the target pressure and the gas pressure at the patient end needs to be reduced, the control module generates a second control instruction, and reduces the acting force of the expiratory valve driving device on the diaphragm of the expiratory valve (the air discharge flow rate of the expiratory branch is increased) and/or reduces the rotating speed of the fan (the air supply flow rate of the inspiratory branch is reduced, and the air supply flow rate of the minimum inspiratory branch is 0) through the second control instruction, so that the pressure at the patient end is reduced.

By way of example, when the patient-side pressure is greater than the target pressure and there is a bleed flow rate (the turbine outlet pressure is greater than the patient-side pressure), then either decreasing the bleed flow rate or increasing the bleed flow rate helps prevent the patient-side pressure from increasing. In other words: if the turbine outlet pressure is higher than the patient end pressure, the air supply flow rate can be reduced by reducing the turbine outlet pressure, so that the pressure at the patient end can be reduced, and the pressure at the patient end can be prevented from increasing; alternatively, reducing the force of the exhalation valve drive mechanism against the exhalation valve diaphragm can increase the exhaust flow rate and also help reduce the pressure at the patient end, preventing the pressure from increasing at the patient end. Thus, when the patient-side pressure is greater than the target pressure and there is an aspiration flow rate: the control module can maintain the turbine state, only reduce the acting force of the expiratory valve driving device on the expiratory valve diaphragm, and increase the flow rate of the exhaust gas, thereby reducing the pressure at the patient end and/or preventing the pressure at the patient end from increasing; the control module can also maintain the state of the expiratory valve, only reduce the rotating speed of the turbine and reduce the flow rate of the air supply, thereby reducing the pressure at the patient end and/or preventing the pressure at the patient end from increasing; the control module may also simultaneously reduce turbine speed (reduce bleed air flow rate) and reduce the force of the exhalation valve driver against the exhalation valve diaphragm (increase bleed air flow rate, increase bleed air), thereby reducing and/or preventing patient end pressure buildup.

As an example, when the patient side pressure is greater than the target pressure and there is no bleed flow rate (0), then the patient side pressure can only be reduced by increasing the bleed of the exhalation valve by reducing the force of the exhalation valve drive against the exhalation valve diaphragm.

For convenience of description, in the following description of the present application, the term "P" is used ₁ "indicates the value of the gas pressure at the outlet of the fan 804 actually measured by the first pressure sensor 805, and is denoted by" P ₂ "represents the patient end gas pressure value measured by the second pressure sensor 817 (i.e., the patient end pressure sensor) as" P ₀ "indicates the target value of the gas pressure at the patient end.

As an example, fig. 2A shows a pressure-time curve during operation of a ventilator provided according to an embodiment of the present application. During inspiration, the gas pressure at the patient end needs to be made to follow the curve S ₁ Gradually rise to introduce the mixed gas into the respiratory organ of the patient. Specifically, during the air suction process, the control module 004 may increase the rotation speed of the fan 804 through a control instruction so as to increase the pressure of the mixed gas output by the fan 804, and the pressure sensor 805 may measure the pressure of the mixed gas output by the fan, when the gas pressure P at the air outlet of the fan is detected ₁ Is greater than the measured gas pressure P at the patient end ₂ In this process, the mixed gas flows through the one-way valve 807 and along the mixed gas path L3 to the patient end to provide respiratory support to the patient. Meanwhile, during inspiration, the control module 004 controls the acting force F of the output end of the driving motor 812 on the diaphragm of the exhalation valve 813 through a control instruction, so that the acting force F is greater than the force F' of the gas in the exhalation pipeline L4 acting on the other side of the diaphragm, and the valve body channel of the exhalation valve 813 is in a disconnected state, so as to prevent the gas in the inspiration process from leaking from the exhalation valve 813.

During the expiration, the gas pressure at the patient end needs to be made to follow the curve S ₂ Gradually decreases to exhaust the gas exhaled by the patient to the atmosphere. Specifically, during exhalation, the control module 004 may instruct the output of the drive motor 812 to gradually reduce the force F against the diaphragm of the exhalation valve 813 via control commands. As the force F is gradually reduced, the diaphragm is gradually moved away from the closure, the valve body passage is gradually opened, and the gas exhaled by the patient is exhausted to the atmosphere via the valve body passage. Meanwhile, during the exhalation process, the control module 004 controls through the control instructionThe rotating speed of the fan enables the gas pressure P1 at the air outlet of the fan to be smaller than the measured pressure P2 at the patient end. The patient's exhaled air cannot flow backwards along the inspiratory air path due to the reverse flow closure of the one-way valve 807. Contaminated air exhaled by the patient is exhausted from the exhalation valve, so that the contaminated exhaled air is prevented from entering the inhalation branch circuit to cause repeated inhalation of the patient or damage to precision components in the respirator by the contaminated air.

The breathing process is a continuously varying process. During the whole breathing process, the control module 004 can detect the measured value P of the gas pressure at the patient end according to the pressure sensor 817 at the patient end ₂ The speed of the fan 804 is adjusted in real time to adjust the flow rate of the bleed air and/or the force F of the drive motor 812 against the diaphragm of the exhalation valve 813 to adjust the flow rate of the bleed air.

In some embodiments, factors in the respiratory system can cause perturbations to the patient end gas, such that the patient end gas measured pressure P ₂ Exceeds the target pressure P ₀ Or is less than the target pressure P ₀ 。

When the measured pressure P is ₂ Exceeds the target pressure P ₀ In time, the control module 004 may generate control instructions and, via the control instructions, decrease the flow rate of the ventilation gas and/or increase the flow rate of the ventilation gas, decrease the flow rate (absolute value) at the patient end, decrease the pressure at the patient end, or prevent the pressure at the patient end from increasing. When the flow rate of the air supply is available, the control module can control the flow rate of the air supply by: controlling at least one of reducing the turbine speed to reduce the flow rate of the supplied air, and reducing the driving force of the expiratory valve driving device on the diaphragm of the expiratory valve to increase the flow rate of the discharged air of the expiratory valve to reduce the flow rate at the patient end. When there is no air flow rate, the control module may: the control reduces the driving force of the expiratory valve driving device on the expiratory valve diaphragm to increase the bleeding flow rate of the expiratory valve, so that the flow rate at the patient end is reduced.

When the measured pressure P of the gas at the patient end ₂ Below the target pressure P ₀ The control module 004 can generate control instructions and increase the flow rate of the air supply and/or decrease the flow rate of the air discharge through the control instructions, increase the flow rate at the patient end, increase the pressure at the patient end, or prevent the pressure at the patient end from decreasing.When there is an exhaust flow rate, the control module may: and controlling at least one of increasing the rotation speed of the turbine to increase the air supply flow rate and increasing the driving force of the exhalation valve driving device on the exhalation valve membrane to reduce the air discharge flow rate of the exhalation valve to increase the patient end flow rate. When there is no bleed flow rate, the control module may: the control increases the turbine speed to increase the flow rate of the air supply, so that the flow rate at the patient end is increased.

As an example, fig. 2B shows a schematic relationship diagram between a target value and an actual measurement value of a pressure time curve of a ventilator provided according to an embodiment of the present application. Referring to fig. 2b, S may represent a target pressure time curve and S' may represent a measured pressure time curve.

At t ₁ At that moment, the measured pressure of the patient-end pressure sensor exceeds the target pressure, then: the control module 004 can generate a control instruction and reduce the acting force F of an output part of the driving motor 812 on the diaphragm of the exhalation valve 813 through the control instruction, so that the valve body channel of the exhalation valve is opened to release a part of gas, and the gas pressure at the patient end is reduced; the control module can also control the turbine to rotate at a reduced speed to reduce the air flow rate so as to reduce the flow rate and the pressure at the patient end.

At t ₂ At the moment, the pressure measured by the patient end pressure sensor is lower than the target pressure, then: the control module 004 can generate a control instruction and increase the rotation speed of the fan 804 through the control instruction so as to increase the gas pressure at the patient end; the control module may also increase the force of the exhalation valve actuator on the exhalation valve diaphragm to decrease the flow rate of the exhaust gas to increase the patient side flow rate and pressure.

The control principle for the exhalation process is the same as or similar to the above-described process principle. For brevity, the regulation of the pressure at the patient end during exhalation is not described in detail.

It should be noted that, in the description of the present application, the "inspiratory flow rate", "inspiratory phase" and "patient in inspiratory process" of the inspiratory gas path are not equal, and the "expiratory flow rate", "expiratory phase" and "patient in expiratory process" are not equal. While fig. 2A and 2B are illustrated, a particular process of operation of the ventilator is described in an exemplary description. The regulation of the fan speed and/or the drive force of the exhalation valve drive by the control module of the present application can be in any process of ventilator operation without affecting the core spirit of the present application.

In some embodiments, when the gas pressure at the patient end does not need to be increased, the control module can control the rotation speed of the fan through a control command, so that the gas pressure P1 at the air outlet of the fan is slightly smaller than the pressure P2 at the patient end. For example, in the exhalation process, the control module can control the rotation speed of the fan through a control command, so that the gas pressure P1 at the air outlet of the fan is slightly less than the pressure P2 at the patient end. On one hand, the gas pressure P1 of the air outlet of the fan is slightly less than the pressure P2 of the patient end, and the gas in the expiration gas path cannot flow back to the inspiration gas path under the one-way throttling action of the one-way valve; on the other hand, the gas pressure P1 of the air outlet of the fan is slightly smaller than the pressure P2 of the patient end, if the pressure value of the patient end needs to be increased at a certain moment in the future, the speed of the fan can be rapidly increased to the required rotating speed, the response speed of the fan is increased, and the response speed of the whole breathing machine is further increased.

For example, when the patient end gas pressure does not need to be increased, the control module may control the rotation speed of the blower according to the control command, so that the gas pressure P1 at the air outlet of the blower is smaller than the patient end pressure P2, and the difference between P1 and P2 may not be greater than a preset pressure difference.

In conclusion, the ventilator provided by the application is provided with the fan and the one-way valve in sequence along the inspiration direction in the expiration air path, the first pressure sensor is arranged at the downstream of the fan and at the upstream of the one-way valve so as to detect the pressure of the air outlet of the fan, the expiration valve and the driving motor are arranged in the expiration air path, and the control module adjusts the rotating speed of the fan and/or the acting force of the driving motor on the diaphragm of the expiration valve in real time according to the measurement signals of the sensors, so that the control of the ventilator is realized. Specifically, when the measured gas pressure at the patient end is smaller than the target pressure and the gas pressure at the patient end needs to be increased, the control module can increase the rotating speed of the fan through a control instruction so as to increase the gas pressure at the patient end; when the measured pressure of the gas at the patient end is larger than the target pressure and the pressure of the gas at the patient end needs to be reduced, the control module reduces the acting force of the output component of the driving motor on the membrane of the expiratory valve through the control instruction, so that the pressure of the gas at the patient end is reduced.

The application provides a breathing machine: on one hand, the air supply flow rate is adjusted by adjusting the rotating speed of the fan, the air release flow rate is adjusted by adjusting the driving force of the expiratory valve driving device on the diaphragm of the expiratory valve, the adjustment of the flow rate of a patient end and the pressure of the patient end is realized, an additional air source is not required to be arranged, an air compressor is omitted, the problem that the pneumatic respirator needs the heavy air source is solved, an additional flow control device (such as a proportional valve) is not required, the control system is simplified, and the cost is reduced; on the other hand, compare in the condition that combines flow control device to control patient end gas pressure through the hierarchical rotational speed of control fan and increase and reduce, the breathing machine that this application provided, control module regulates and control fan rotational speed and/or driving motor to the effort of expiratory valve in real time according to the measuring signal of sensor, fan rotational speed and driving motor all can be along with patient end pressure measured value real-time change to the effort of expiratory valve, do not need additionally to add flow control device in the mixed gas circuit of inhaling the module, the structure of inhaling the gas circuit is simpler, the breathing machine overall control scheme is also simpler, and the breathing machine wholly has higher response speed.

Furthermore, a safety valve in the respirator can protect a patient from overvoltage and power failure; the inspiration keeping valve can realize inspiration keeping, and can ensure that certain patients in need can complete sufficient oxygenation process in an inspiration phase through inspiration keeping; the mouth end flow sensor (namely the second flow sensor 811) can more accurately detect the tidal volume of the patient and feed the tidal volume back to the breathing machine control module in real time, so that the human-computer synchronization effect is better; the purging component can effectively prevent water drops in the sampling pipe of the mouth end flow sensor from being condensed to influence the measurement precision; high-pressure gas adjusting part can carry out steady voltage and current-limiting to high-pressure oxygen source, simultaneously, still is provided with low-pressure oxygen source interface on the high-pressure gas adjusting part, when hospital oxygen source pressure is not enough or does not have the high-pressure oxygen source, can let in low-pressure oxygen at low-pressure oxygen source interface and continue to treat the patient, still includes the atomizing runner among the high-pressure gas adjusting part, and the atomizing runner can provide atomizing oxygen source for the patient that needs medication.

As an example, fig. 3 shows a schematic hardware structure diagram of a ventilator 001 provided in accordance with an embodiment of the present application. The inspiratory module of ventilator 001 may include blower 400 and one-way valve 807. In some embodiments, the inspiratory module can further comprise a filter assembly 200, a sound attenuating and mixing device 100, a shock absorbing assembly 300, a first pressure sensor, a first flow sensor, an inspiratory hold valve, a safety valve, an oxygen battery, and/or a high pressure gas regulating device. The exhalation module of ventilator 001 may include an exhalation valve and an exhalation valve drive motor.

By way of example, fig. 4A illustrates a connection diagram of a filtering assembly 200, a sound-deadening and mixing device 100, a shock-absorbing assembly 300, and a fan 804 according to an embodiment of the present disclosure. FIG. 4B illustrates a partial cross-sectional view of a muffling and mixing apparatus 100 and a shock assembly 300 provided in accordance with an embodiment of the present application. By way of example, fig. 4C illustrates a partial cross-sectional view of a shock assembly 300 and a fan 804 provided in accordance with an embodiment of the present application.

Referring to fig. 4C, the blower 804 may include an intake vent 410 and an exhaust vent 420. The end of the fan 804 to which the motor is connected is 430. The fan 804 is at least partially within the shock box 310.

The shock absorbing assembly 300 may include a shock absorbing case 310 and a shock absorbing member 320. The damping assembly 300 mainly uses damping material to wrap and support the turbo fan so as to play a role in damping vibration, and also plays a role in sealing connection with the air outlet of the silencing and mixing device so as to smoothly introduce the air flow output by the silencing and mixing device into the turbo fan.

The shock absorbing members 320 are filled in a space between the blower 804 and the inner wall of the shock absorbing case 310. In one aspect, the shock absorbing member 320 may provide support for the fan 804; on the other hand, the vibration absorbing member 320 can reduce vibration of the fan 804 during operation. In some embodiments, the shock absorbing member 320 may include shock absorbing cotton 321 having a shock absorbing function. The number of the shock-absorbing cottons 321 may be plural. The damping cotton 321 may wrap a portion of the fan 804 where vibration is generated. In some embodiments, the shock absorbing member 320 may further include a shock absorbing silicone pad 322. The shock absorbing silicone pad 322 may be disposed between the blower 804 and the end cap 530.

The shock-absorbing box 310 has a cavity structure. The cavity structure is configured to receive the damper 320 and the fan 804. The shock-absorbing case 310 may include a first opening 311 and a second opening 312. The first opening 311 corresponds to the air inlet 410 of the fan 804, and is communicated with the air inlet 410 of the fan 804, so that the target gas is guided to the air inlet 410 of the fan 804 through the first opening 311. The second opening 312 corresponds to the air outlet 420 of the blower 804, and the second opening 312 is configured to allow the target gas flowing out of the air outlet 420 to flow out of the blower assembly 001. As an example, the arrows in FIG. 4C show the flow direction l of the target gas ₀ 。

In some embodiments, the ventilator 001 further comprises an air outlet duct 510. The air outlet pipe 510 has a hollow pipe structure and includes an air outlet pipe air inlet end 511 and an air outlet pipe air outlet end 512. The air inlet end 511 of the air outlet pipe is communicated with the air outlet 420. The air outlet pipe air outlet end 512 is located outside the shock absorption box 310, wherein a first detection interface 513 is arranged at the part, located outside the shock absorption box 310, of the air outlet pipe 510. The first pressure sensor 805 for measuring the pressure at the air outlet of the air blower 804 can measure the air pressure at the air outlet of the air blower 804 through the first detection interface 513.

In some embodiments, an air inlet connection portion 314 is disposed in the shock-absorbing box 310 at a position corresponding to the first opening 311, the air inlet connection portion 314 has a hollow pipe structure, and the first opening 311 is an inlet of the hollow pipe structure.

The shock absorbing assembly 300 may further include an air intake connection pipe 520. The air inlet connection pipe 520 includes a hollow pipe structure. Both ends of the air inlet connection pipe 520 are respectively connected to the air inlet connection portion 314 and the air inlet 410 of the fan, so as to communicate the fan connection portion 314 with the air inlet 410 of the fan.

In some embodiments, the shock box 310 further includes a third opening 313. The shock absorbing assembly 300 may further include an end cap 530, the end cap 530 is disposed at one end of the shock absorbing box 310 close to the third opening 313, the end cap 530 is connected to the shock absorbing box 310 to close the third opening 313, wherein a fourth opening 531 (the fourth opening 531 is shown in fig. 1) is disposed on the end cap 530 to allow one end 430 of the fan 804 connected with the motor to protrude.

In some embodiments, the first opening 311 is disposed on the first outer surface 319 of the shock box 310. The sound attenuating mixing device 100, located upstream of the shock absorbing assembly 300, may be attached to the first outer surface 319. Wherein the gas outlet of the silencing and mixing device 100 can communicate with the first opening 311.

In some embodiments, the shock assembly 300 may further include a seal ring 540. A sealing ring 540 may be disposed between the end cap 530 and the shock-absorbing box 310 to improve sealability. As an example, the damper box 310 may be provided with a packing installation groove. The packing 540 may be installed in the packing installation groove.

Referring to fig. 4B, the muffling and mixing apparatus 100 is configured to reduce noise of the target gas. The noise-reduction mixing apparatus 100 may be provided at one side of the shock-absorbing assembly 300. For example, the sound attenuating assembly 300 may be disposed at one side of the first opening 311 of the shock absorbing assembly 300. The target gas may be in the direction l shown in FIG. 4B ₀ And (4) flowing. Along the direction l of the target gas flow ₀ The noise-damping mixing device 100 may be disposed upstream of the shock-absorbing assembly 300.

With continued reference to FIG. 4B, the acoustic mixing apparatus 100 may include a first passage 10, a second passage 20, and a mixing chamber 30. The first passage 10 and the second passage 20 communicate with the mixing chamber 30. The first passage may constitute a part of an air flow passage in the air gas path L1 shown in fig. 1, the second passage may constitute a part of an oxygen flow passage in the oxygen gas path L2 shown in fig. 1, and the mixing chamber may constitute the mixing chamber 803 shown in fig. 1.

The first channel 10 is configured to guide the first gas from the first gas channel inlet 11 to the mixing chamber 30. As an example, the first gas may be air. The second channel 20 is configured to direct a second gas from a second gas channel inlet 21 to the mixing chamber 30. As an example, the second gas may be oxygen. The first gas and the second gas are mixed in the mixing chamber 30 as the target gas. The mixing chamber 30 includes a mixing chamber outlet 31, and the mixing chamber outlet 31 communicates with the first opening 311 of the damper assembly 300 to guide the target gas to the damper assembly 300.

Specifically, the silencing and mixing device 100 may include a silencing box 110 and a silencing part 120. The silencing element 120 may be arranged inside the silencing box 110 forming said first passage 10 and/or said mixing chamber 30. The silencer 120 may be made of a silencing material (e.g., silencing cotton), and the silencer 120 is configured to eliminate noise of the first gas.

As an example, fig. 4D shows an isometric view of a sound damping box 110 provided according to an embodiment of the present application, and fig. 4E shows an isometric view of another orientation of a sound damping box 110 provided according to an embodiment of the present application.

Referring to fig. 4D and 4E, the sound-deadening box 110 includes a first wall plate 81, a second wall plate 82, a third wall plate 83, a fourth wall plate 84, and a fifth wall plate 85. Wherein the first wall plate 81, the second wall plate 82, the third wall plate 83, the fourth wall plate 84, and the fifth wall plate 85 enclose a main chamber of the sound-deadening box 110 and form a main chamber inlet 86. The first wall plate 81 is opposite the fourth wall plate 84, the second wall plate 82 is opposite the main chamber inlet 86, and the third wall plate 83 is opposite the fifth wall plate 85.

Be provided with separation structure 89 in the main cavity room, separation structure 89 will the main cavity room is separated into first subchamber Q ₁ And a second sub-chamber Q ₂ . The first gas inlet is arranged to form the first sub-chamber Q ₁ On the wall panel of (2). As an example, the first gas inlet 11 is a through hole structure on the fifth wall plate 85. A plurality of noise damping members may be provided in the first sub-chamber Q ₁ Forming said first channel 10 and said mixing chamber 30. For example, the plurality of silencersThe member may in turn be disposed between the second wall plate 82 and the main chamber inlet 86. The first sub-chamber Q ₁ And may be divided into a first portion and a second portion. At least one silencing element 120 is arranged in said first part forming said first passage 10 and at least one silencing element 120 is arranged in said second part forming said mixing chamber 30. The outer contour of the silencer closest to the main chamber inlet 86 matches the main chamber inlet 86 and substantially seals the main chamber inlet 86, wherein the silencer is provided with a through hole structure, which is the mixed gas outlet 31. For example, in the embodiment shown in FIG. 4B, 5 muffling elements X ₁ 、X ₂ 、X ₃ 、X ₄ And X ₅ Are sequentially arranged in the first sub-cavity Q along the flowing direction of the first gas ₁ Forms said first channel 10. Silencing part X ₆ And a silencing member X ₇ Are sequentially arranged in the first sub-cavity Q ₁ Forming the mixing chamber 30. Silencing part X ₆ With silencing parts X on both sides ₅ And a silencing member X ₇ Enclosing said mixing chamber 30. Silencing part X ₆ Is provided with an opening to communicate with the first passage 10. Silencing part X ₇ Is disposed at the end closest to the main chamber inlet 86. Silencing part X ₇ Is sized to substantially match the main chamber inlet 86. Thus, the silencing element X ₇ Substantially blocking the main chamber inlet 86. The mixing cavity air outlet 31 is arranged on the silencing part X ₇ The above.

With continued reference to fig. 4D and 4E, the second subchamber Q is formed ₂ The wall of the chamber wall of (2) is provided with an outer conduit (92). One end of the outer pipe 92 is the second gas inlet 21, and the other end is the second sub-chamber Q ₂ And (4) communicating. As an example, the outer pipe 92 may be disposed on the first wall plate 81 and protrude from the first wall plate 81.

By way of example, the second gas inlet 21 is disposed at an end remote from the main chamber inlet 86. Thus, on the one hand, the distance between the second gas inlet 21 and the mixed gas outlet 31 is increased, increasing the length of the second channel 20; on the other hand, the installation position is reserved for other parts on the oxygen path, so that the structure of the respirator provided with the silencing box is more compact.

In some embodiments, the sound damping box 110 may further include a receiving cavity 114. The accommodation chamber 114 may be disposed upstream of the first gas inlet 11 in the direction of the first gas flow. One end of the accommodating chamber 114 is communicated with the first gas inlet 11, and the other end is communicated with the atmosphere. The receiving cavity 114 may be a filter assembly receiving cavity. The receiving cavity 114 is configured to receive a filter assembly. The filter assembly may filter the first gas. The filter assembly is at least partially within the receiving cavity 114. The receiving cavity 114 can be defined by the fifth wall 85 and the wall 87 surrounding the outer contour edge of the fifth wall 85. The receiving cavity 114 is substantially rectangular. A catch 94 may be provided on wall 87. A snap may be provided on the filter assembly and snap into the snap groove 94 to secure the filter assembly within the receiving cavity 114.

In some embodiments, the sound damping cartridge 110 may further include a mounting portion 95. The mounting portion 95 is provided at one end of the main chamber inlet 86. For example, the mounting portion 95 may include at least one mounting ear disposed circumferentially around the primary chamber inlet 86. The mounting portion 95 may be provided with mounting holes configured to allow fasteners to pass therethrough and mount the acoustic mixing apparatus 100 to the shock box. In some embodiments, the sound attenuating assembly and the shock absorbing assembly may be of a unitary design, however, the unitary design may increase the cost of manufacturing, assembly, maintenance, etc. Taking the maintenance cost as an example, if the shock absorption assembly breaks down, the silencing assembly integrally designed with the shock absorption assembly needs to be replaced, and the maintenance cost is increased. This application is connected amortization subassembly and damper through installation department, and amortization subassembly and damper are independent each other, can realize amortization subassembly and damper's modular design, have improved manufacturability, have reduced and have generated assembly cost of maintenance.

In some embodiments, the sound damping box 110 may further include a packing member installation groove 118. The seal mounting slot 118 may be disposed at one end of the primary chamber inlet 86 and disposed around the primary chamber inlet 86. A sealing member 40 (e.g., a packing) may be installed in the sealing member installation groove 118 to improve sealability of the connection between the sound-damping box 110 and the shock-absorbing box.

In some embodiments, the sound-deadening cartridge 110 may further include a negative pressure detection port 51. As an example, the negative pressure detection port 51 is provided on the second wall plate 82. In some embodiments, the silencing and mixing device 100 may further include a negative pressure detecting device 50, and the negative pressure detecting device 50 may access the first channel 10 through the negative pressure detecting port 51 to measure the negative pressure in the first channel 10.

In some embodiments, the sound damping box 110 may also include mounting feet 88. By way of example, mounting feet 88 may be provided on third wall panel 83. The mounting feet 88 may attach the sound damping box to the support unit.

Referring to fig. 4B, the fan assembly 002 may also include a seal 40. A seal 40 may be disposed between the acoustic mixing apparatus 100 and the shock box 310 to prevent leakage of gas as it flows from the acoustic mixing apparatus 100 to the shock assembly 300. As an example, the sealing member 40 may be installed in the installation groove 118 on the sound-deadening box 110.

Referring to fig. 4A, a filter assembly 200 is disposed along the first gas passageway upstream of the first gas inlet 11 and is configured to filter the first gas. By way of example, the filter assembly may be used to filter dust and germs from a first gas (e.g., air). By way of example, fig. 4F illustrates a schematic structural diagram of a filter assembly 200 provided in accordance with an embodiment of the present application. Specifically, the filter assembly 200 may include a filter assembly mounting housing 210, a primary filter pulp 220, a high efficiency filter pulp 230, and a gasket 240.

The filter assembly mounting housing 210 includes a mounting housing inlet 211, a mounting housing outlet 212, and a mounting cavity 213 communicating the mounting housing inlet 211 and the mounting housing outlet 212.

The filter assembly mounting housing 210 is designed with a snap 214. When the filter assembly 200 is assembled with the sound damping box 110, the latch 214 is engaged with the latch groove 94 of the sound damping box 110. With this design, on the one hand, the filter assembly 200 is fixed in the filter assembly receiving cavity 114; on the other hand, the packing 240 is compressed between the sound-deadening cartridge 110 and the filter element mounting case 210, improving the sealing performance between the sound-deadening cartridge 110 and the filter element mounting case 210.

The primary filter wool 220 and the high efficiency filter wool 230 are disposed within the filter assembly mounting housing 210 and are configured to filter the first gas.

The gasket 240 is disposed at one end of the mounting case outlet 212 and configured to enhance sealability at a connection portion of the filter assembly mounting case 210 and the sound-deadening cartridge 110, thereby preventing unfiltered first gas from entering the first channel 10.

As an example, fig. 5A shows a schematic structural diagram of a high pressure gas regulating device 600 provided according to the present application. Specifically, the high pressure gas adjusting apparatus 600 may include a pressure adjusting assembly 610, a flow rate adjusting assembly 620, and a connection pipe 630.

By way of example, fig. 5B illustrates a schematic structural diagram of a pressure adjustment assembly 610 provided in accordance with an embodiment of the present application. Pressure regulation assembly 610 may include a pressure regulation valve 611 and a first support drain 612. As an example, the pressure regulating valve 611 may be a pressure maintaining valve. The pressure maintenance valve is mounted on the first support drain 612. In some embodiments, the pressure regulation assembly 610 may further include an inlet fitting 613, a first outlet fitting 614, a second outlet fitting 615, an on-off valve 616, a pressure sensor 617, and/or a constrictor valve 618.

By way of example, fig. 5C illustrates a partial cross-sectional view of a pressure adjustment assembly 610 provided in accordance with an embodiment of the present application, and fig. 5D illustrates a partial cross-sectional view of a first support drain 612 provided in accordance with an embodiment of the present application.

Referring to fig. 5C and 5D, the first support drain 612 includes a first outer surface 612-a, a second outer surface 612-B, a third outer surface 612-C, a fourth outer surface 612-D, a fifth outer surface 612-E, and a sixth outer surface 612-F, wherein: the first outer surface and the second outer surface are opposed, the third outer surface and the fourth outer surface are opposed, and the fifth outer surface and the sixth outer surface are opposed.

The first support drainage member 612 includes a first chamber 6121, and a first flow passage 6122 and a second flow passage 6123 which are communicated with the first chamber 6121, wherein a first end 611-1 of the pressure regulating valve 611 is installed in the first chamber 6121, wherein an end face of the first end 6111 is spaced from the bottom of the first chamber 6121 by a preset distance, so that a drainage cavity 6124 is formed between the first end 6111 and the side wall of the first chamber 6121, an air inlet of the pressure regulating valve 611 is communicated with the drainage cavity 6124, wherein the first flow passage 6122 is communicated with the drainage cavity 6124, the first support drainage member 612 drains gas from the air outlet of the pressure regulating valve 611 through the first flow passage 6122 and via the drainage cavity 6124, the second flow passage 6123 corresponds to and is communicated with the air outlet of the pressure regulating valve 611, and the first support drainage member 612 drains the gas flowing from the air outlet of the pressure regulating valve 611 to a first target pipeline outside the pressure regulating assembly 610 through the second flow passage 6123. As an example, the first target circuit may be an oxygen circuit in an inspiratory circuit of a ventilator.

In some embodiments, the inlet of the first flow passage 6122 is disposed at the first outer surface 612-a of the first support baffle 612, and the outlet of the first flow passage 6122 is disposed at the sidewall of the first chamber 6121 and near the bottom of the first chamber 6121; the outlet of the second flow passage 6123 is disposed on the second outer surface 612-B of the first support drain 612, the second outer surface 612-B is opposite to the first outer surface 612-a, the inlet of the second flow passage 6123 is disposed on the sidewall of the first chamber 6121 and is close to the inlet of the first chamber 6121, wherein the inlet of the first chamber 6121 is on the fifth outer surface 612-E of the first support drain 612.

In some embodiments, the first support drain 612 further comprises a second chamber 6125, a third flow passage 6126, and a fourth flow passage 6127. Wherein the second chamber 6125 is in communication with the second flow passage 6123. The third flow passage 6126 is communicated with the second chamber 6125. The second chamber 6125 is configured to provide an installation space for the flow-regulating member 618, and a flow-limiting flow passage 6180 is formed between the second chamber 6125 and the first end 618 of the flow-regulating member 618, one end of the flow-limiting flow passage 6180 is communicated with the second flow passage 6123, the other end of the flow-limiting flow passage 6180 is communicated with the third flow passage 6126, the flow-limiting flow passage 6180 is configured to guide the gas in the second flow passage 6123 to the third flow passage 6126, wherein the flow-regulating member 618 is at least partially installed in the second chamber 6125, the distance between the outer wall of the first end 618-1 of the flow-regulating member 618 and the inner wall of the second chamber 6125 can be adjusted so as to form a size-adjustable flow-limiting flow passage 6180 between the first end 618-1 of the flow-regulating member 618 and the inner wall of the second chamber 6125, and a sealing member 619 is disposed between the second end 618-2 of the flow-regulating member 618 and the inner wall of the second chamber 6125 to prevent the gas in the flow-limiting flow passage 6180 from leaking; the third flow passage 6126 is configured to direct gas to the inlet of the on-off valve 616; and the fourth flow passage 6127 is configured to direct the gas flowing out of the outlet of the on-off valve 616 to a second target line outside the pressure regulating assembly 610. Illustratively, the first end 618-1 of the flow-regulating member 618 is tapered, and the second end 618-2 of the flow-regulating member 618 is threadedly coupled to the inner wall of the second chamber 6125. As an example, the on-off valve 616 may be a fogging on-off valve. As an example, the flow regulator 618 may be a needle valve. As an example, the second target circuit may be an aerosolization branch or a purge branch in a ventilator.

In some embodiments, the second chamber 6125 includes a through-hole structure beginning at the sixth outer surface 612-F of the first support drain 612 and ending at a sidewall of the second flow passage 6123; the third flow passage 6126 comprises a through hole structure starting from the third outer surface 612-C of the first support drain 612 and ending at the inner wall of the second chamber 6125; the fourth flow passage 6127 starts from the third outer surface 612-C of the first support drain 612 and ends at the second outer surface 612-B of the first support drain 612, wherein the fourth flow passage 6127 includes a first blind hole structure starting from the third outer surface 612-C and a second blind hole structure starting from the outer surface 612-B, and wherein the bottom of the first blind hole structure is communicated with the bottom of the second blind hole structure.

By way of example, fig. 5E illustrates a partial cross-sectional view of a pressure adjustment assembly 610 provided in accordance with an embodiment of the present application. The first support drainage member 612 further comprises a pressure detection duct 6128, the pressure detection duct 6128 is communicated with the drainage cavity 6124, and the pressure detection device 616 can measure the pressure at the air inlet end of the pressure regulating valve 611 through the pressure detection duct 6128, wherein the pressure detection duct 6128 comprises a through hole structure starting from the third outer surface 612-C of the first support drainage member 612 and ending at the inner wall of the first cavity 6121.

As an example, fig. 5F illustrates a schematic structural diagram of a flow regulating assembly 620 provided according to an embodiment of the present application. The flow regulating assembly 620 includes a flow regulating valve 621 and a second support drain 622. By way of example, fig. 5G illustrates a partial cross-sectional view of a second support drain 622 provided in accordance with an embodiment of the present application.

Referring to fig. 5F and 5G, the second supporting drain 622 includes a first connection chamber 6221 and a second connection chamber 6222, the inlet 6221-1 of the first connection chamber 6221 is a high pressure gas inlet, and the sidewall of the second connection chamber 6222 is provided with a low pressure gas inlet 6222-3.

The second support drain 622 includes a first outer surface 622-A, a second outer surface 622-B, a third outer surface 622-C, a fourth outer surface 622-D, a fifth outer surface 622-E, and a sixth outer surface 622-F, the first outer surface and the fourth outer surface being opposed, the second outer surface and the fifth outer surface being opposed, the third outer surface and the sixth outer surface being opposed, wherein the high pressure gas inlet 6221-1 and the low pressure gas inlet 6222-3 are disposed at the first surface 622-A, the first connecting chamber outlet 6221-2 and the second connecting chamber inlet 6222-1 are disposed at the second surface 622-B adjacent to the first surface 622-A, and the second connecting chamber outlet 6222-2 is disposed at the fourth surface 622-D opposed to the second surface 622-B.

The second connecting cavity 6222 includes an inlet air passage, an outlet air passage, and a buffer air passage disposed between the inlet air passage and the outlet air passage, wherein the inlet air passage and the outlet air passage are cylindrical air passages, and the diameter of the inlet air passage is smaller than that of the outlet air passage.

The second support drain 622 can also include mounting holes 6223 through which fasteners can be passed to mount the flow regulating assembly 620 to the target site.

A flow regulating valve 621 may be installed on the second supporting drain 622. The flow regulating valve 621 is configured to regulate the flow rate of the high-pressure gas to a target flow rate. The inlet of the flow regulating valve 621 communicates with the outlet 6221-2 of the first connecting chamber. The air outlet of the flow regulating valve 621 is communicated with the inlet 6222-1 of the second connecting cavity.

The flow regulation component 620 may also include a flow sensor 623. The flow sensor 623 may be in communication with the outlet 6222-2 of the second coupling chamber and configured to measure the flow of gas out of the outlet 6222-2 of the second coupling chamber. In some embodiments, the outlet end of the flow sensor 623 may also be connected to a transition tube 624.

The flow regulation assembly 620 may also include a low pressure gas fitting 625 mounted at the low pressure gas port 6222-3. Of course, in some embodiments, a high pressure gas connector 626 may be connected to the high pressure gas inlet.

With continued reference to fig. 5A, one end of the connection pipe 630 is communicated with the gas outlet of the second flow passage, and the other end is communicated with the high-pressure gas inlet of the flow regulating valve, and is configured to guide the gas flowing out of the gas outlet of the pressure regulating valve to the flow regulating valve.

To sum up, the high-pressure gas adjusting device 600 that this application provided has atomizing gas outlet and atomizing on-off valve in its design, and atomizing gas outlet is linked together with the atomizing joint, and the atomizing joint, atomizing gas outlet and atomizing on-off valve have constituteed the atomizing branch road, and according to patient's needs, the break-make of atomizing branch road is atomized to the atomizing on-off valve control, has realized oxygen branch road and atomizing branch road integrated design. The outlet of the high pressure gas regulating device 600 is designed with a low pressure oxygen inlet connector, the low pressure oxygen inlet connector is communicated with the low pressure oxygen connector, and when the hospital can not provide high pressure oxygen or the pressure of the high pressure oxygen source is insufficient under some special conditions, the low pressure oxygen connector delivers oxygen for the patient to treat.

As an example, fig. 6A shows a schematic structural diagram of a suction holding valve 808 provided according to an embodiment of the present application. The suction holding valve 808 may include a valve body 710, a diaphragm 720, and a diaphragm mount 730.

The valve body 710 comprises an inlet cavity 711 and an outlet cavity 712, the inlet cavity 711 and the outlet cavity 712 can be communicated to form a valve body channel 740, wherein an opening and closing port 750 is arranged in the valve body channel 740. As an example, the open-close port 750 may be an outlet of the intake chamber 711.

The diaphragm mounting seat 730 includes a control air cavity 731, the control air cavity 731 includes a first opening 7311 and a second opening 7312, the diaphragm 720 is connected to the diaphragm mounting seat 730 and seals the first opening 7311, the second opening 7312 is configured to allow the output portion 791 of the driving unit 790 to pass through, wherein, after the output portion 791 enters the control air cavity 731 through the second opening 7312, a force can be applied to the diaphragm 720 to drive the diaphragm 720 to seal the opening 750, thereby cutting off the valve body passage 740.

The side wall of the air inlet cavity 711 is provided with a first interface 701, the side wall of the control air cavity 731 is provided with a second interface 702, the first interface 701 and the second interface 702 can be communicated by a communication unit 780 so as to guide the air in the air inlet cavity 711 to the control air cavity 731, and the air guided into the control air cavity 731 exerts force on the diaphragm 720 so as to assist the driving unit 790 in controlling the opening and closing of the valve body channel 740.

In some embodiments, the area of the working portion of the diaphragm 720 is larger than the area of the opening and closing port 750, such that the force exerted on the diaphragm 720 by the gas directed into the control chamber is greater than the force exerted on the diaphragm 720 by the gas in the gas inlet chamber 711, thereby driving the diaphragm 720 to close the opening and closing port 750.

In some embodiments, the second opening 7312 opens onto the outer surface 735 of the diaphragm mount 730. The drive unit 790 may include fixation portions 792, which may be fixedly attached to the outer surface 735. Wherein a sealing member 760 may be disposed between the fixing portion 792 and the outer surface 735 and around the second opening 7312 to prevent gas leakage from within the control chamber. As an example, the driving unit 790 may be an electromagnet device, the output part thereof may be a magnet, and the fixing part thereof may include a coil.

In some embodiments, the communication unit 780 may include an on-off valve. As an example, the switching valve may be a two-position three-way valve.

Referring to fig. 3, the inspiratory hold valve 808 is primarily used to block the inspiratory branch when the patient requires inspiratory hold, ensuring that the pressure in the patient's airway is maintained at a certain value for a certain period of time without decay. The suction hold valve 808 may be in communication with the one-way valve 807 at a front end and the suction valve 8210 at a rear end. The valve sealing force of the air suction holding valve 8210 comes from the combined action of the electromagnet and the air pressure, so that the problem that the failure rate of an independent electromagnet valve is high due to excessive heating of power, and the problem that the valve sealing effect is poor due to independent dependence on gas is solved. The holding valve 808 is controlled by the switch valve 8212 to control the valve-closing pressure of the holding valve, and the valve may be a two-position three-way valve. When the valve sealing is needed, the electromagnet is powered on, the air suction holding valve is powered on by the switch valve 8212, the valve sealing cavity is inflated, and the air suction holding valve 808 is sealed. When the air suction holding is finished, the electromagnet is powered off, the switch valve 8212 for the air suction holding valve is powered off, the valve sealing cavity is empty, the valve sealing cavity is rapidly deflated, and the valve port is opened. Note that the air release resistance of the valve sealing cavity cannot be too large, otherwise, the air pressure in the valve sealing cavity can generate a damping effect on the diaphragm due to too slow release, and the opening speed of the valve port is further influenced.

As an example, fig. 6B shows a schematic operation principle of a safety valve 809 provided according to an embodiment of the present application. The hardware structure of the safety valve shown in fig. 6B may be the same as that of the expiratory hold valve shown in fig. 6A, and is not described again for brevity.

Referring to fig. 3, the safety valve 809 functions to provide a breathing pathway to the patient to prevent the patient from a apneic event when the ventilator is powered down or otherwise fails. The relief valve 809 operates on the same principle as the suction hold valve 808. The front end of the safety valve 809 is connected by a bypass from the rear end of the suction holding valve 808, and the rear end of the safety valve 809 is empty. When the respirator normally works, the electromagnet of the safety valve 809 is electrified, the switch valve 8213 for the safety valve is electrified, and the safety valve 809 seals the valve. When the respirator is powered off or fails, the electromagnet of the safety valve is powered off, the switch valve 8213 for the safety valve is powered off, the safety valve 809 is opened, and the patient breathes freely.

According to the air suction holding valve and/or the safety valve, air in the air inlet cavity can be guided to the control air cavity, so that the auxiliary driving unit 790 controls the membrane, and the power consumption of the system is reduced.

With continued reference to fig. 3, the purge module 005 may include a gas capacitance assembly 8101, a pressure sampling connection one 8102, a pressure sampling connection two 8103, and a purge switch valve 8104. The purging switch 8104 is mainly used for controlling the on-off of the air volume component 8101 during inflation, when a patient inhales, the purging switch 8104 is turned on, and the air passage in the respirator is communicated with the air volume component 8101 to start inflation. When the patient begins to exhale, due to the reduction of airway pressure in the respirator, the purge switch 8104 is closed, and the gas in the gas capacity component 8101 is prevented from reversely losing. The first pressure sampling joint 8102 and the second pressure sampling joint 8103 are located at the interfaces inside the respirator, and are respectively communicated with the air outlet of the air capacitor assembly 8101 and a pressure sensor (not shown) on the ventilation control board 8507 through a Y-shaped three-way joint. The first pressure sampling joint 8102 and the second pressure sampling joint 8103 are positioned on the interface outside the shell of the respirator and are communicated with two sampling pipes of a patient end flow sensor.

With continued reference to fig. 3, the ventilator 001 may also include a zero check valve 8214, a blood oxygen test connector 8215 and/or a CO2 test connector 8216. The zero calibration valve 8214 is communicated with the front end of each pressure sensor and used for performing timing zero calibration on the pressure sensors, and the phenomenon that the error of measured data is overlarge due to zero drift of the pressure sensors is avoided. Blood sample test connection 8215 and CO2 test connection 8216 are used to monitor the blood oxygen content or CO2 content, respectively, of the patient.

The ventilator 001 may also include a peripheral accessory module. The peripheral accessory module can comprise external accessories such as a patient end flow sensor, a breathing pipeline, a humidifier and the like.

A control module in the ventilator 001 is mainly used for carrying out ventilation control, ventilation monitoring and ventilation control on the ventilator. Specifically, referring to fig. 3, the control modules in the ventilator 001 may include a capacitive PCBA board 8501, a power control board 8502, a turbine control board 8503, an ad-DC power module 8504, an ac outlet 8505, a power switch 8506, and a ventilation control board 8507. Electric capacity PCBA board 8501 mainly used stabilizes turbine supply voltage, guarantees that the turbine operates steadily, and electric capacity size and quantity can suitably increase and decrease as required. The power management board 8502 is mainly used to manage charging of the battery and to transmit power to the ventilation control board 8507. The turbine control plate 8503 is used primarily to control the operational bleed of the turbine. The AC-DC power module 8504 is mainly used to convert the input 220V AC power into DC power usable by the ventilator. The AC socket 8505 is an external 220V alternating current interface. The power switch 8506 is used to control the on/off of the ventilator. The aeration control panel 8507 is mainly used to control and monitor the whole working process and state of the ventilator to ensure the normal operation of the ventilator.

The ventilator 001 may also include a display module. The display module is mainly used for displaying the setting parameters and the breathing parameters of the patient in real time during treatment so as to assist a doctor in observing and diagnosing the treatment condition of the patient in real time.

In conclusion, upon reading the present detailed disclosure, those skilled in the art will appreciate that the foregoing detailed disclosure can be presented by way of example only, and not limitation. Those skilled in the art will appreciate that the present application is intended to cover various reasonable variations, adaptations, and modifications of the embodiments described herein, even though not expressly described herein. Such alterations, improvements, and modifications are intended to be suggested by this disclosure, and are within the spirit and scope of the exemplary embodiments of this disclosure.

The terminology used in the present application and the drawings accompanying the present application are for the purpose of describing particular example embodiments only and are not intended to be limiting. Furthermore, certain terminology has been used in this application to describe embodiments of the disclosure. For example, "one embodiment," "an embodiment," and/or "some embodiments" means that a particular feature, structure, or characteristic described in connection with the embodiment can be included in at least one embodiment of the present disclosure. Therefore, it is emphasized and should be appreciated that two or more references to "an embodiment" or "one embodiment" or "an alternative embodiment" in various portions of this specification are not necessarily all referring to the same embodiment. Furthermore, the particular features, structures, or characteristics may be combined as suitable in one or more embodiments of the disclosure.

It should be appreciated that in the foregoing description of embodiments of the disclosure, various features are sometimes grouped together in a single embodiment, figure, or description thereof for the purpose of streamlining the disclosure aiding in the understanding of the subject disclosure. This application is intended to cover such departures from the present disclosure as come within known or customary practice in the art to which this invention pertains. This is not to be taken as an admission that any of the features of the claims are essential, and it is fully possible for a person skilled in the art to extract some of them as separate embodiments when reading the present application. That is, the embodiments in the present application may also be understood as an integration of a plurality of sub-embodiments. And each sub-embodiment described herein is equally applicable to less than all features of a single foregoing disclosed embodiment.

In some embodiments, numbers expressing quantities or properties used to describe and claim certain embodiments of the application are to be understood as being modified in some instances by the term "about", "approximately" or "substantially". For example, "about," "approximately," or "substantially" can mean a ± 20% variation of the value it describes, unless otherwise specified. Accordingly, in some embodiments, the numerical parameters set forth in the written description and attached claims are approximations that may vary depending upon the desired properties sought to be obtained by a particular embodiment. In some embodiments, numerical parameters should be construed in light of the number of reported significant digits and by applying ordinary rounding techniques. Notwithstanding that the numerical ranges and parameters setting forth the broad scope of the embodiments of the application are approximations, the numerical values set forth in the specific examples are reported as precisely as possible.

Each patent, patent application, publication of a patent application, and other material, such as articles, books, descriptions, publications, documents, articles, and the like, cited herein is hereby incorporated by reference. All matters hithertofore set forth herein except as related to any prosecution history, may be inconsistent or conflicting with this document or any prosecution history which may have a limiting effect on the broadest scope of the claims. Now or later associated with this document. For example, if there is any inconsistency or conflict in the description, definition, and/or use of terms associated with any of the contained materials with respect to the description, definition, and/or use of terms associated with this document, the terms in this document shall prevail.

Finally, it should be understood that the embodiments of the application disclosed herein are illustrative of the principles of the embodiments of the present application. Other modified embodiments are also within the scope of the present application. Accordingly, the disclosed embodiments are presented by way of example only, and not limitation. Those skilled in the art can implement the invention in the present application in alternative configurations according to the embodiments in the present application. Thus, embodiments of the present application are not limited to those precisely described in the application.

Claims

1. A ventilator, comprising:

a gas circuit module comprising an inhalation gas circuit module and an exhalation gas circuit module, wherein the inhalation gas circuit module comprises a blower and a one-way valve configured to allow one-way flow of gas in a direction toward a patient, wherein the one-way valve is downstream of the blower, and the exhalation gas circuit module comprises an exhalation valve and an exhalation valve driving device; and

the control module is connected with the pressure sensor and the flow sensor, receives measurement signals from the pressure sensor and the flow sensor when in work, generates a control command according to the measurement signals, and regulates and controls the rotating speed of the blower and/or the acting force of the expiratory valve driving device on the expiratory valve diaphragm through the control command so as to control the work of the respirator,

when the gas pressure at the patient end is lower than the target pressure, the control module generates a first control instruction, and increases the rotating speed of the fan and/or the acting force of the exhalation valve driving device on the exhalation valve diaphragm through the first control instruction so as to increase the gas pressure at the patient end,

when the gas pressure at the patient end is higher than the target pressure, the control module generates a second control instruction, and reduces the acting force of the expiratory valve driving device on the diaphragm of the expiratory valve and/or reduces the rotating speed of the fan through the second control instruction so as to reduce the gas pressure at the patient end.

2. The ventilator of claim 1, wherein:

when the gas pressure at the patient end is higher than the target pressure and the air supply flow rate is available in the air suction circuit, the control module reduces the gas pressure at the patient end by at least one of the following methods:

the rotation speed of the fan is controlled to be reduced to reduce the flow rate of the air supply in the air suction path, and,

controlling and reducing the acting force of the expiratory valve driving device on the expiratory valve diaphragm to increase the flow rate of the expiratory gas in the expiratory gas circuit;

when the gas pressure at the patient end is higher than the target pressure and the gas supply flow rate is not available in the inspiration gas circuit, the control module controls to reduce the acting force of the expiration valve driving device on the expiration valve membrane so as to increase the gas discharge flow rate in the expiration gas circuit, so that the gas pressure at the patient end is reduced;

when the patient end gas pressure is less than the target pressure and there is a flow rate of exhaust gas in the expiratory gas circuit, the control module increases the patient end gas pressure by at least one of:

controlling the increase in the rotational speed of the blower to increase the flow rate of the delivered air in the air-intake path, and,

controlling and increasing the acting force of the expiratory valve driving device on the expiratory valve diaphragm to reduce the flow rate of the expiratory gas in the expiratory gas circuit;

when the gas pressure at the patient end is lower than the target pressure and the air discharge flow rate in the expiration air circuit is not high, the control module controls the rotation speed of the fan to be increased so as to increase the air discharge flow rate in the inspiration air circuit, and therefore the gas pressure at the patient end is increased.

3. The ventilator of claim 1, wherein:

the inspiratory circuit module comprises an air circuit, an oxygen circuit and a mixing circuit, wherein the air circuit comprises an air flow channel, the air flow channel is communicated with an air inlet and a mixing chamber, the air flow channel is configured to guide air from the air inlet to the mixing chamber, the oxygen circuit comprises an oxygen flow channel, the oxygen flow channel is communicated with the oxygen inlet and the mixing chamber, the oxygen flow channel is configured to guide oxygen from the oxygen inlet to the mixing chamber, the air and the oxygen are mixed into mixed gas in the mixing chamber, the mixing circuit comprises a mixed gas flow channel, the mixed gas flow channel is communicated with the mixing chamber and a patient interface, the mixed gas flow channel is configured to guide the mixed gas from the mixing chamber to the patient interface, and the blower and the one-way valve are both disposed in the mixing circuit;

the at least one pressure sensor comprises a first pressure sensor, wherein the first pressure sensor is connected to the inspiratory gas path downstream of the blower and upstream of the one-way valve, the first pressure sensor configured to measure a gas pressure within the inspiratory gas path downstream of the blower and upstream of the one-way valve; and

the patient-side gas pressure is obtained by the control module based on measurement data of a second pressure sensor, wherein:

the second pressure sensor is connected to an air suction path at the downstream of the one-way valve,

The second pressure sensor is connected to the expiratory air passage, and/or

The second pressure sensor is connected to the patient end airway.

4. The ventilator of claim 3, wherein said oxygen inlet comprises a hyperbaric oxygen inlet, said inspiratory circuit module further comprising a hyperbaric oxygen regulating device connected in the oxygen circuit downstream of said hyperbaric oxygen inlet and upstream of said mixing chamber, wherein said hyperbaric oxygen regulating device comprises:

the pressure regulating device comprises a pressure regulating valve and a first supporting drainage piece, wherein the first supporting drainage piece comprises a first chamber, a first flow passage and a second flow passage, the first flow passage and the second flow passage are communicated with the first chamber, the first end of the pressure regulating valve is installed in the first chamber, the end face of the first end is spaced from the bottom of the first chamber by a preset distance, so that a drainage cavity is formed between the first end and the side wall of the first chamber, the air inlet of the pressure regulating valve is communicated with the drainage cavity, the first flow passage is communicated with the drainage cavity, the first supporting drainage piece conducts air to the air inlet of the pressure regulating valve through the first flow passage and the drainage cavity, the second flow passage corresponds to and is communicated with the air outlet of the pressure regulating valve, and the first supporting drainage piece conducts the air flowing out of the air outlet of the pressure regulating valve to an air passage at the downstream of the pressure regulating assembly through the second flow passage; and/or

Flow control device supports the drainage piece including flow control valve and second, wherein, the second supports the drainage piece and includes first connection chamber and second connection chamber, the entry in first connection chamber is the high-pressure gas entry, the lateral wall in second connection chamber is provided with the low-pressure gas entry, flow control valve installs on the second supports the drainage piece, flow control valve's air inlet with the export intercommunication in first connection chamber, flow control valve's gas outlet with the entry intercommunication in second connection chamber.

5. The ventilator of claim 3, wherein said inspiratory circuit module further comprises an acoustic mixing device, said acoustic mixing device comprising a first channel, a second channel, and a mixing chamber, said first channel and said second channel being in communication with said mixing chamber, said first channel forming at least a portion of said air circuit, said second channel forming at least a portion of said oxygen circuit, said mixing chamber forming said mixing chamber, said mixing chamber comprising a mixing chamber outlet, said mixing chamber outlet being in communication with an air intake of said blower,

the silencing and mixing device comprises a silencing box and a plurality of silencing pieces, wherein the silencing pieces are arranged in the silencing box, so that the silencing and mixing device forms the first channel and the mixing cavity, and the silencing pieces are made of silencing materials and are configured to eliminate noise of gas entering the fan through the silencing and mixing device.

6. The ventilator of claim 5, wherein said inspiratory circuit module further comprises a filter device connected in the air circuit downstream of the air inlet and upstream of the sound suppression cartridge,

wherein the filtering device comprises an installation shell, primary filter cotton, high-efficiency filter cotton and a sealing gasket, the installation shell comprises an installation shell inlet, an installation shell outlet and an installation cavity communicated with the installation shell inlet and the installation shell outlet, the primary filter cotton and the high-efficiency filter cotton are arranged in the installation shell and are configured to filter air passing through the filtering device, the sealing gasket is arranged at one end of the installation shell outlet, the installation shell is designed with a buckle,

the silencing box further comprises a filtering device accommodating cavity, the filtering device accommodating cavity is configured to accommodate the filtering device, a clamping groove is formed in a wall plate of the filtering device accommodating cavity, the clamping groove is configured to allow the buckle of the mounting shell to be clamped in, and therefore the filtering device is fixed in the filtering device accommodating cavity.

7. The ventilator of claim 1, wherein said inspiratory circuit module further comprises a shock assembly comprising a shock box and a shock absorber,

the shock absorption box is provided with a cavity structure, the fan is at least partially arranged in the shock absorption box,

the shock absorbing member is filled in a space between the fan and the inner wall of the shock absorbing box to reduce the vibration of the fan during operation,

the shock absorption box comprises a first opening and a second opening, the first opening corresponds to the air inlet of the fan and is communicated with the air inlet of the fan so as to guide the mixed gas from the first opening to the air inlet of the fan, and the second opening corresponds to the air outlet of the fan and is configured to allow an air outlet connecting pipe connected to the air outlet of the fan to penetrate so as to guide the mixed gas flowing out of the air outlet to an air path downstream of the fan.

8. The ventilator of claim 7, wherein the shock assembly further comprises:

one end of the air inlet connecting pipe is connected with the air inlet connecting part of the damping box, and the other end of the air inlet connecting pipe is connected with the air inlet of the fan, so that the air inlet connecting part of the damping box is communicated with the air inlet of the fan, wherein the air inlet connecting part of the damping box is of a hollow pipe structure, and the first opening is an inlet of the hollow pipe structure; and/or

And one end of the air outlet adapter tube is connected with an air outlet of the fan, a first detection interface is arranged on the part of the air outlet adapter tube, which is positioned outside the damping box, the at least one pressure sensor comprises a first pressure sensor connected to a third gas pipeline at the downstream of the fan and at the upstream of the patient interface, and the first pressure sensor is connected with the first detection interface and is connected to the third gas pipeline through the first detection interface.

9. The ventilator of claim 1, wherein said inspiratory circuit module further comprises an oxygen concentration sensor connected to the inspiratory circuit downstream of the one-way valve, said oxygen concentration sensor configured to measure an oxygen concentration in a gas within the inspiratory circuit,

the air suction circuit module further comprises an air suction circuit outlet connecting piece, the air suction circuit outlet connecting piece is provided with an air flow channel, a second detection interface is arranged on the side wall of the air flow channel, and the oxygen concentration sensor is connected with the second detection interface and connected to the air suction circuit through the second detection interface.

10. The ventilator of claim 1, wherein said pneumatic circuit module further comprises:

a safety valve connected to the inspiratory air path downstream of the one-way valve, the safety valve configured to provide a breathing pathway to the patient to prevent a patient apnea event when the ventilator is powered down or fails;

the inspiration keeping valve is connected in the inspiration gas path, and is configured to cut off the inspiration branch when the patient needs inspiration keeping, so that the pressure in the airway of the patient is kept at a preset value within a certain time without attenuation;

the zero calibration valve is connected with more than one target pressure sensor and is configured to perform timing zero calibration on the target pressure sensors, so that the phenomenon that the error of measured data is overlarge due to zero drift of the target pressure sensors is avoided;

a blood oxygen test connector configured to allow access to a blood oxygen test device for monitoring blood oxygen content of a patient;

CO ₂ a test joint configured to allow CO ₂ The test device is switched on to thereby detect CO in the gas exhaled by the patient ₂ Monitoring the content; and/or

And the purging module is used for giving a purging airflow to the sensor sampling pipe during operation so as to prevent a pollution source from blocking the sensor sampling pipe or polluting the sensor through the sensor sampling pipe.