CN113730754B - Air pressure control jet ventilation auxiliary device for hard bronchoscope - Google Patents

Air pressure control jet ventilation auxiliary device for hard bronchoscope Download PDF

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Publication number
CN113730754B
CN113730754B CN202111073144.6A CN202111073144A CN113730754B CN 113730754 B CN113730754 B CN 113730754B CN 202111073144 A CN202111073144 A CN 202111073144A CN 113730754 B CN113730754 B CN 113730754B
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electromagnetic valve
interface
air
bottle
central temporary
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CN113730754A (en
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彭建良
吕静
单立刚
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Second Affiliated Hospital Of Xiamen Medical College
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Second Affiliated Hospital Of Xiamen Medical College
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/267—Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor for the respiratory tract, e.g. laryngoscopes, bronchoscopes
    • A61B1/2676—Bronchoscopes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L2/00—Methods or apparatus for disinfecting or sterilising materials or objects other than foodstuffs or contact lenses; Accessories therefor
    • A61L2/16—Methods or apparatus for disinfecting or sterilising materials or objects other than foodstuffs or contact lenses; Accessories therefor using chemical substances
    • A61L2/20—Gaseous substances, e.g. vapours
    • A61L2/202—Ozone
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/0003—Accessories therefor, e.g. sensors, vibrators, negative pressure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/10—Preparation of respiratory gases or vapours
    • A61M16/105—Filters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/10—Preparation of respiratory gases or vapours
    • A61M16/1075—Preparation of respiratory gases or vapours by influencing the temperature
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/10—Preparation of respiratory gases or vapours
    • A61M16/14—Preparation of respiratory gases or vapours by mixing different fluids, one of them being in a liquid phase
    • A61M16/16—Devices to humidify the respiration air
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3331—Pressure; Flow
    • A61M2205/3334—Measuring or controlling the flow rate
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3368—Temperature
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/75—General characteristics of the apparatus with filters

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  • Health & Medical Sciences (AREA)
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  • Veterinary Medicine (AREA)
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Abstract

The application discloses a hard bronchoscope air pressure control jet ventilation auxiliary device, which comprises a power supply module, a Y-shaped tube, a micro-pressure switch, an electromagnetic valve group and a central temporary bottle, wherein the Y-shaped tube is connected with the main body through a micro-pressure switch; one end of the Y-shaped tube is provided with a ventilation interface, and the other end of the Y-shaped tube is connected with a central temporary bottle; the electromagnetic valve group comprises a high-frequency electromagnetic valve group and a large-diameter electromagnetic valve; the high-frequency electromagnetic valve group is connected between the air source and the central temporary bottle; the large-diameter electromagnetic valve is connected between the central temporary bottle and the air inlet of the first air filter; the micro-pressure switch is provided with a first pressure interface and a second pressure interface, is normally open and is connected between the output end of the power module and the input end of the electromagnetic valve bank to control the electromagnetic valve bank to be electrified or powered off; the air flow in the respiratory tract of the patient enters the central temporary bottle, is output to the first air filter through the large-diameter electromagnetic valve to be filtered and then discharged, and the phase air flow exhaled by the patient can be filtered and then discharged through the first air filter, so that air pollution can be effectively prevented.

Description

Air pressure control jet ventilation auxiliary device for hard bronchoscope
Technical Field
The application relates to the technical field of medical equipment, in particular to a hard bronchoscope air pressure control jet ventilation auxiliary device.
Background
Hard bronchoscope is one of the main tools of modern interventional pneumology, and is used together with bendable bronchoscope and other various instruments, thus being an interventional means for diagnosing and treating airway diseases safely and effectively. General anesthesia can be performed by a professional anesthesiologist, and diagnosis and treatment can be performed, and one of the important points is that mechanical ventilation is ensured to be safe and controllable. Jet ventilation is an efficient and convenient ventilation mode, and is favored by respiratory endoscopists because the jet ventilation ventilator maintains the openness of the airway. The entrainment characteristics of the jet orifice by the jet ventilation venturi effect require that the airway be kept open to atmosphere to ensure adequate entrainment. The openness of the airway, the gas of the patient breathes out in the air all, sprays and ventilates in the unknown state of disease diagnosis, easily causes the pollution of consulting room air, and the medical staff who participates in diagnosis and treatment exposes the risk greatly. At present, the concentration of O2 and CO2 in the respiratory tract cannot be accurately monitored and analyzed so as to accurately regulate and control the jet ventilation parameters. If jet ventilation is performed for a long time, respiratory mucosa dryness, postoperative hypothermia and other complications easily occur, the jet ventilation time needs to be strictly controlled, and the implementation of partial diagnosis and treatment is affected.
Disclosure of Invention
Aiming at the defects in the prior art, the application aims to provide a hard bronchoscope air pressure control jet ventilation auxiliary device which can effectively prevent the breathing gas of a patient from being discharged into the air.
The technical scheme adopted by the application is as follows:
the hard bronchoscope air pressure control jet ventilation auxiliary device comprises a power supply module, a Y-shaped tube, a micro-pressure switch, an electromagnetic valve group and a central temporary bottle; one end of the Y-shaped tube is provided with two ventilation interfaces which are correspondingly connected with two side ports of the hard bronchoscope, and the other end of the Y-shaped tube is connected with a central temporary bottle; the electromagnetic valve group comprises a high-frequency electromagnetic valve group and a large-diameter electromagnetic valve; the high-frequency electromagnetic valve group is connected between the air source and the central temporary bottle; the large-diameter electromagnetic valve is connected between the central temporary bottle and the air inlet of the first air filter, and the air outlet of the first air filter is connected with the atmosphere; the micro-pressure switch is provided with a first pressure interface used for being connected with the injection pipeline and a second pressure interface used for being connected with the inclined port of the hard bronchoscope, is normally open and is connected between the output end of the power supply module and the input end of the electromagnetic valve group so as to control the electromagnetic valve group to be electrified or powered off;
when the jet ventilation and gas phase suction are performed, the micro-pressure switch is closed, the electromagnetic valve group is electrified to enable the gas source to be communicated with the central temporary bottle, and the first air filter is disconnected with the central temporary bottle;
when the jet ventilation breathes out the gaseous phase, the micro-pressure switch disconnection, solenoid valve group outage makes the air supply and central temporary bottle disconnection, and first air cleaner and central temporary bottle intercommunication.
Further comprises a protective bottle, a second vacuum pump and CO 2 Detection port and O 2 The concentration detector, the inlet end of protection bottle is connected on the tie point of Y type pipe and central authorities' bottle of staying temporarily, the end of giving vent to anger of protection bottle is connected with the inlet end of second vacuum pump, and the end of giving vent to anger of second vacuum pump connects gradually CO 2 Detection port and O 2 The concentration detector is connected with a central temporary bottle.
Further, the air source comprises an oxygen source and an air source, the high-frequency electromagnetic valve group comprises an electromagnetic valve B and an electromagnetic valve C, the oxygen source is connected with the central temporary bottle through the electromagnetic valve B, and the air source is connected to a connecting point of the oxygen source and the electromagnetic valve B through the electromagnetic valve C.
Further, a second interface of the electromagnetic valve B is connected with an oxygen source, a first interface of the electromagnetic valve B is connected with a central temporary bottle, and a third interface of the electromagnetic valve B is connected with air; when the electromagnetic valve B is electrified, the second interface of the electromagnetic valve B is communicated with the first interface, and when the electromagnetic valve B is powered off, the second interface of the electromagnetic valve B is communicated with the third interface.
Further, the air source is an incubator, the air inlet end of the incubator is communicated with the atmosphere through a second air filter, and the air outlet end of the incubator is connected with a second interface of the electromagnetic valve B through the electromagnetic valve C.
The device further comprises a first vacuum pump, wherein the air inlet end of the first vacuum pump is connected with the air outlet end of the incubator, the air outlet end of the first vacuum pump is connected with the second interface of the electromagnetic valve C, the first interface of the electromagnetic valve C is connected with the second interface of the electromagnetic valve B, and the third interface of the electromagnetic valve C is connected with the air inlet end of the incubator; when the electromagnetic valve C is electrified, the second interface is communicated with the first interface, and when the electromagnetic valve C is deenergized, the second interface is communicated with the third interface.
Further, the humidifier further comprises an electromagnetic valve A and a humidifying bottle, wherein a second interface of the electromagnetic valve A is connected with an oxygen source, a first interface of the electromagnetic valve A is connected with an air inlet end of the humidifying bottle, and an air outlet end of the humidifying bottle and a third interface of the electromagnetic valve A are connected with a second interface of the electromagnetic valve B.
Further, a first interface of the large-diameter electromagnetic valve is connected with an air outlet end of the incubator, a second interface of the large-diameter electromagnetic valve is connected with the central temporary bottle, and a third interface of the large-diameter electromagnetic valve is connected with the first air filter; when the large-diameter electromagnetic valve is electrified, the first interface is communicated with the second interface, and when the large-diameter electromagnetic valve is powered off, the second interface is communicated with the third interface.
Further, a temperature and humidity detection box, an air drying agent and a flow sensor are sequentially connected between the third interface of the large-diameter electromagnetic valve and the first air filter.
Further, the device also comprises an ozone generator, and the ozone generator is connected with the temperature box.
Additional aspects and advantages of the application will be set forth in part in the description which follows, and in part will be obvious from the description, or may be learned by practice of the application.
Drawings
In order to more clearly illustrate the embodiments of the present application or the technical solutions in the prior art, the drawings used in the description of the embodiments or the prior art will be briefly described below. Like elements or portions are generally identified by like reference numerals throughout the several figures. In the drawings, elements or portions thereof are not necessarily drawn to scale.
FIG. 1 is a schematic diagram of a hard bronchoscope air pressure control jet ventilation auxiliary device according to an embodiment of the present application;
FIG. 2 is an enlarged view of a portion of FIG. 1;
FIG. 3 is a schematic diagram of a micro-voltage switch according to an embodiment of the present application;
FIG. 4 is a schematic circuit diagram of a micro-voltage switch and solenoid valve assembly according to an embodiment of the present application;
fig. 5 is a schematic diagram of a connection structure of a temperature and humidity controller according to an embodiment of the present application;
fig. 6 is a schematic circuit diagram of a temperature and humidity controller according to an embodiment of the present application.
Wherein, the hard bronchoscope 1, the Y-shaped tube 2, the central temporary bottle 3, the humidifying bottle 4, the first vacuum pump 5, the incubator 6, the ozone generator 7, the second air filter 8, the heater 9, the first air filter 10, the air drying agent bottle 11, the temperature and humidity detection box 12 and O 2 Concentration detector 13, CO 2 The device comprises a detection port 14, a second vacuum pump 15, a protection bottle 16, a flow sensor 17, a power module 18, a micro-pressure switch 19 and a temperature and humidity controller 20.
In the figure, the arrow direction represents the air flow direction.
Detailed Description
Embodiments of the technical scheme of the present application will be described in detail below with reference to the accompanying drawings. The following examples are only for more clearly illustrating the technical aspects of the present application, and thus are merely examples, and are not intended to limit the scope of the present application.
It is noted that unless otherwise indicated, technical or scientific terms used herein should be given the ordinary meaning as understood by one of ordinary skill in the art to which this application belongs.
Referring to fig. 1 to 6, the air pressure control jet ventilation auxiliary device of the hard bronchoscope comprises a power module 18, a Y-shaped tube 2, a micro-pressure switch 19, an electromagnetic valve group and a central temporary bottle 3; one end of the Y-shaped tube 2 is provided with two ventilation interfaces which are correspondingly connected with two side ports of the hard bronchoscope 1, and the other end of the Y-shaped tube 2 is connected with a central temporary bottle 3; the electromagnetic valve group comprises a high-frequency electromagnetic valve group and a large-diameter electromagnetic valve; the high-frequency electromagnetic valve group is connected between the air source and the central temporary bottle 3; the large-diameter electromagnetic valve is connected between the central temporary bottle 3 and the air inlet of the first air filter 10, and the air outlet of the first air filter 10 is connected with the atmosphere; the micro-pressure switch 19 is provided with a first pressure interface for being connected with an injection pipeline and a second pressure interface for being connected with an inclined port of the hard bronchoscope 1, and the micro-pressure switch 19 is normally open and is connected between the output end of the power module 18 and the input end of the electromagnetic valve group so as to control the electromagnetic valve group to be electrified or powered off; when the jet ventilation and gas phase suction are performed, the micro-pressure switch 19 is closed, the electromagnetic valve group is electrified to enable the gas source to be communicated with the central temporary storage bottle 3, and the first air filter 10 is disconnected with the central temporary storage bottle 3; when the ventilation phase is injected, the micro-pressure switch 19 is turned off, the solenoid valve group is turned off to disconnect the air source from the central temporary storage bottle 3, and the first air filter 10 is communicated with the central temporary storage bottle 3.
When in use, the two ventilation interfaces of the Y-shaped tube 2 are respectively connected with the two side ports of the hard bronchoscope 1, the first pressure interface of the micro-pressure switch 19 is connected with the jet ventilation ventilator through the jet ventilation pipeline, and the second pressure interface of the micro-pressure switch 19 is connected with the inclined port of the hard bronchoscope 1; when the jet ventilation and gas phase suction are performed, the jet airflow enters the hard bronchoscope 1 through the first pressure interface and the second pressure interface of the micro-pressure switch 19, meanwhile, the micro-pressure switch 19 is closed under the pressure action, the electromagnetic valve group is electrified to enable the air source to be communicated with the central temporary storage bottle 3, so that air is introduced into the central temporary storage bottle 3, and when the jet airflow enters the hard bronchoscope 1, venturi effect is generated to roll and suck the air in the central temporary storage bottle 3, so that ventilation efficiency can be greatly improved; when the ventilation and breathing phases are sprayed, the micro-pressure switch 19 is restored to the off state, the electromagnetic valve group is powered off to disconnect the air source from the central temporary reserved bottle 3, air cannot enter the central temporary reserved bottle 3, the first air filter 10 is communicated with the central temporary reserved bottle 3 under the action of the large-diameter electromagnetic valve, air flow in the respiratory tract of a patient enters the central temporary reserved bottle 3, and the air flow is output to the first air filter 10 through the large-diameter electromagnetic valve and is filtered and then discharged, and the air flow of the breathing phases of the patient can be filtered and then discharged through the arrangement of the first air filter 10, so that air pollution can be effectively prevented.
To facilitate detection of exhaled air, a protective bottle 16, a second vacuum pump 15, CO are also included 2 Detection ports 14 and O 2 The concentration detector 13, the air inlet end of the protection bottle 16 is connected to the connection point of the Y-shaped tube 2 and the central temporary bottle 3, the air outlet end of the protection bottle 16 is connected to the air inlet end of the second vacuum pump 15, and the air outlet end of the second vacuum pump 15 is sequentially connected to CO 2 Detection ports 14 and O 2 The concentration detector 13 is then connected to the central temporary storage bottle 3.
The second vacuum pump 15 adopts a miniature diaphragm pump direct current air pump, the model of which is EDLP600-D24B, the flow rate is 600ml/min, and the vacuum degree is 0.04kpa. O (O) 2 The concentration detector 13 may be an intelligent portable oxygen analyzer ZY12C oxygen analyzer. By providing a second vacuum pump 15, a part of the air flow exhaled by the patient directly enters the central temporary flask 3, and another small part passes through CO under the action of the second vacuum pump 15 2 Detection ports 14 and O 2 The concentration detector 13 performs CO 2 Concentration and O 2 After concentration inspection, the mixture enters the central temporary storage bottle 3, and CO of the air flow exhaled by the patient can be realized 2 Concentration and O 2 Monitoring concentration provides data support for anesthesiologists to adjust jet ventilator ventilation parameters to facilitate accurate regulation of jet ventilation parameters
The micro-pressure switch 19 adopts an Ilicis differential pressure switch, 500-2500 PA (engineering style), and the pressure range is 500-2500 PA. The high-frequency electromagnetic valve group comprises an electromagnetic valve B and an electromagnetic valve C, wherein the electromagnetic valve B is connected in parallel, the electromagnetic valve C is connected in parallel, after the electromagnetic valve B, the electromagnetic valve C and the large-diameter electromagnetic valve are connected in parallel, the input end of the electromagnetic valve is connected with one pole of the power module 18 through the micro-pressure switch 19, and the output end of the electromagnetic valve is connected with the other pole of the power module 18. The micro-pressure switch 19 is normally open, and when the micro-pressure switch 19 is disconnected, the electromagnetic valve group is powered off, and a second interface of the electromagnetic valve group is connected with a third interface; when the micro-pressure switch 19 is closed, the electromagnetic valve group is electrified, and a second interface of the electromagnetic valve group is connected with the first interface.
The air source comprises an oxygen source and an air source, wherein the oxygen source is connected with the central temporary storage bottle 3 through the electromagnetic valve B, and the air source is connected to the connection point of the oxygen source and the electromagnetic valve B through the electromagnetic valve C.
Specifically, the second interface of the electromagnetic valve B is connected with an oxygen source, the first interface of the electromagnetic valve B is connected with the central temporary bottle 3, and the third interface of the electromagnetic valve B is connected with air; when the electromagnetic valve B is electrified, the second interface of the electromagnetic valve B is communicated with the first interface, and oxygen enters the central temporary bottle 3 from the second interface and the first interface of the electromagnetic valve B; when the electromagnetic valve B is powered off, the second interface is communicated with the third interface, and oxygen is discharged from the second interface and the third interface of the electromagnetic valve B.
And the air source is connected with the air inlet end of the humidifying bottle 4, the air outlet end of the humidifying bottle 4 and the third interface of the solenoid valve A are connected with the second interface of the solenoid valve B. When humidification is not needed, the second interface of the electromagnetic valve A is connected with the third interface, and oxygen output by the oxygen source is directly input into the second interface of the electromagnetic valve B through the second interface and the third interface of the electromagnetic valve A; when the input oxygen is required to be humidified, the second interface of the electromagnetic valve A is connected with the first interface, oxygen output by an oxygen source is input into the humidifying bottle 4 through the second interface of the electromagnetic valve A and the first interface for humidification, and after humidification, the oxygen is output to the second interface of the electromagnetic valve B through the output end of the humidifying bottle 4.
The air source is an incubator 6, the air inlet end of the incubator 6 is communicated with the atmosphere through a second air filter 8, and the air outlet end of the incubator 6 is connected with a second interface of the electromagnetic valve B through an electromagnetic valve C. Air is input into the incubator 6 through the second air filter 8, is output to the second interface of the solenoid valve B through the solenoid valve C, and enters the central temporary storage bottle 3 after being mixed with oxygen.
The temperature box 6 is also provided with a heater 9, the heater 9 is a PTC heater 9, the model of the PTC heater 9 is CSL028-150W, AC220V, specification 150 x 220mm, and capacity is about 5L; the heater 9 heats the air in the incubator 6 by blowing hot air into the incubator 6. The heated gas enters the central temporary storage bottle 3 through the electromagnetic valve C and the electromagnetic valve B.
Through setting up humidification bottle 4 and heater 9 respectively, can carry out humidification to the gas that lets in the central temporary bottle 3, be favorable to protecting patient's air flue mucous membrane, maintain normothermia.
Humidification and warming may be controlled by a temperature and humidity controller 20. Specifically, the temperature and humidity controller 20 is electrically connected to the heater 9 and the solenoid valve a, respectively, and the temperature and humidity controller 20 controls the heater 9 and the solenoid valve a to control heating and humidification of the gas.
Specifically, the temperature and humidity controller 20 is provided with a temperature sensor and a humidity sensor, and has a specification of 1.5m temperature +1.5HT211, an input voltage of 220VAC and an output voltage of 220VAC. The temperature sensor and the humidity sensor are respectively used for detecting the temperature and the humidity of the gas, and sending the detection results to the temperature and humidity controller 20, and the temperature and humidity controller 20 controls the heater 9 and the electromagnetic valve A according to the detection results. If the heating temperature is set to be 30-35 ℃, and the humidity is set to be 70-95 RH%; namely: if the temperature sensor detects that the gas temperature is lower than 30 ℃, the temperature and humidity controller 20 controls the PTC heater 9 to start so as to heat the air, and if the temperature sensor detects that the gas temperature is higher than 35 ℃, the temperature and humidity controller 20 controls the PTC heater 9 and the PTC heater 9 to stop heating; if the humidity sensor detects that the gas humidity is lower than 70RH%, the second interface of the control electromagnetic valve A is connected with the first interface of the control electromagnetic valve A, oxygen is led into the humidifying bottle 4, and distilled water is used for gas humidification; if the humidity sensor detects that the gas humidity is higher than 95RH%, the second interface of the control electromagnetic valve A is connected with the third interface of the control electromagnetic valve A, so that oxygen is directly input into the electromagnetic valve B.
The air inlet end of the first vacuum pump 5 is connected with the air outlet end of the incubator 6, the air outlet end of the first vacuum pump 5 is connected with the second interface of the electromagnetic valve C, the first interface of the electromagnetic valve C is connected with the second interface of the electromagnetic valve B, and the third interface of the electromagnetic valve C is connected with the air inlet end of the incubator 6; when the electromagnetic valve C is electrified, the second interface of the electromagnetic valve C is communicated with the first interface, and air in the incubator 6 sequentially enters the electromagnetic valve B through the second interface and the first interface of the electromagnetic valve C under the action of the first vacuum pump 5, so that air required by breathing is provided for a patient; when the electromagnetic valve C is powered off, the second interface is communicated with the third interface, and air in the incubator 6 returns to the incubator 6 for circulation under the action of the first vacuum pump 5 through the second interface and the third interface of the electromagnetic valve C.
The model of the first vacuum pump 5 is VN-C1/24V, the flow is 15L/min, the power is 10w, and the vacuum degree is-80 kpa.
The model of the large-diameter electromagnetic valve D is DVG342R-5G-10,1 inch, and the diameter area is 210-235 mm 2 Converted into a round shape, the inner diameter D is approximately equal to 16.36 mm-17.30 mm, and the diameter D is approximately equal to DC24V. The first interface of the large-diameter electromagnetic valve D is connected with the air outlet end of the incubator 6, and the second interface of the large-diameter electromagnetic valve D is connected with the central temporary bottle 3The third interface of the large-diameter electromagnetic valve is connected with the first air filter 10; when the large-diameter electromagnetic valve is electrified, the first interface is communicated with the second interface, so that air in the incubator 6 is guided into the central temporary bottle 3; when the large-diameter electromagnetic valve is powered off, the second interface is communicated with the third interface, and air flow in the central temporary bottle 3 is led out to the first air filter 10 for filtering and then is discharged.
In order to further detect the exhaled air flow, a temperature and humidity detection box 12, an air drying agent bottle 11 and a flow sensor 17 are sequentially connected between the third interface of the large-diameter electromagnetic valve D and the first air filter 10. The capacity of the temperature and humidity controller is 250ml, a temperature sensor and a humidity sensor which are arranged in the temperature and humidity detection box 12 are arranged on the temperature and humidity controller 20, the temperature and humidity of the exhaled air flow are detected, the monitoring result is sent to the temperature and humidity controller 20, and the temperature and humidity of the exhaled air flow are regulated by the temperature and humidity controller 20 through controlling the on-off of the electromagnetic valve A and the heater. The air desiccant bottle 11 has a capacity of about 250ml and acts to dry the flow stream to ensure proper use of the flow controller. The flow sensor 17 adopts a microminiature gas flow controller of MF4000 series, and the specification is MF4008-10L/min.
For the purpose of sterilizing the line through which the exhaled air flows, an ozone generator 7 is also included, which ozone generator 7 is connected to the inlet end of the incubator 6.
After the use of one case is finished, the pipeline behind the air drying agent bottle 11 can be disconnected, the output end of the air drying agent bottle 11 is connected with one ventilation interface of the Y-shaped pipe 2, and the other ventilation interface of the Y-shaped pipe 2 is connected with the incubator 6; a Y-shaped pipe 2, a central temporary bottle 3, a large-diameter electromagnetic valve D, pipelines between a temperature and humidity detection box 12 and an air drying agent bottle 11, a protection bottle 16, a second vacuum pump 15 and CO 2 Detection ports 14 and O 2 The pipelines between the concentration detectors 13 are all communicated with the incubator 6, ozone is generated by the ozone generator 7 and is input into the incubator 6, and the pipelines through which the expired air flows are automatically disinfected, so that cross infection is prevented.
Furthermore, the micro-pressure switch 19 can be manually controlled to enable the electromagnetic valve B, the electromagnetic valve C and the large-diameter electromagnetic valve D to be electrified, and the pipelines among the incubator 6, the first vacuum pump 5, the electromagnetic valve C, the electromagnetic valve B, the central temporary storage bottle 3 and the Y-shaped pipe 2 are conducted so as to disinfect the pipeline through which air flows, thereby further preventing cross infection.
The electromagnetic valve B and the electromagnetic valve C can adopt two-position three-way electromagnetic valves with the model VT307-5G-02 and the working voltage is 220VAC.
In practical applications, several switches may be provided, such as A, B, C, D, 1, 2, X. A: a power supply 24VDC for controlling the large-diameter electromagnetic valve D, the electromagnetic valve B1, the electromagnetic valve B2, the electromagnetic valve C1 and the electromagnetic valve C2; b: a power supply 24VDC controlling the first vacuum pump 5 and the second vacuum pump 15; c: 220VAC of power supply, controlling a temperature and humidity controller, controlling the PTC heater 9 and controlling a 220VAC high-frequency electromagnetic valve; d: 220VAC of power supply, control ozone generator 7; 1. the switch of the large-diameter electromagnetic valve D can be independently controlled; 2. the controllable micro-pressure switch 19 is manually short-circuited; x: the second vacuum pump 15 can be controlled on and off.
The working procedure is as follows:
1. the whole machine is powered on, the flow sensor 17 preheats for about 10min, and is connected with wall oxygen, wall air and jet ventilator jet pipeline (inner diameter 5mm, outer diameter 8 mm);
2. the keys A, B, 1, X are turned to ON position, and the rest are in OFF state;
3. the jet ventilation is started, the air pressure of the air suction phase jet pipeline is rapidly increased, the micro-pressure switch 19 is driven to be in short circuit, and the large-diameter electromagnetic valve controlled by the key A and the electromagnetic valve groups C1 and C2 are started;
4. the first vacuum pump 5 sucks warm air in the incubator 6, mixes the warm air with humidified/non-humidified oxygen through the high-frequency electromagnetic valve sets C1 and C2 and pushes the mixture to the central temporary bottle 3;
5. the jet air flow is jetted from the outlet of the jet connector of the rigid bronchoscope, under the action of Venturi effect, the air around the jet orifice is sucked, and under the action of atmospheric pressure, the warm mixed gas in the central temporary bottle 3 is pushed to the rigid bronchoscope;
6. the jet ventilation and gas suction are finished, the micro-pressure switch 19 is turned off, and the large-diameter electromagnetic valve and the high-frequency electromagnetic valve groups C1 and C2 are closed; under the comprehensive action of respiratory muscles such as the intercostal muscles of the chest and the diaphragm, the lung elastically retracts, the air in the respiratory tract exhales, and the air flows through the central temporary bottle 3, the large-diameter electromagnetic valve, the temperature and humidity detection box 12, the air drying agent bottle 11 and the flow sensor 17 in sequence, and finally is discharged into a special exhaust gas pipeline in a consulting room after being treated by an air filter;
7. the second vacuum pump 15 is continuously operated with the suction phase + the exhaust phase. The second vacuum pump 15 draws the mouth, the air outlet locates in the central temporary bottle 3, the air outlet pipeline connects a protective bottle 16, can connect PETCO2 sampling tube on the pipeline, monitor PETCO2 (end carbon dioxide of expiration); in addition, the air outlet pipeline is connected with an intelligent portable oxygen analyzer ZY12C oxygen analyzer, and O2 concentration change is monitored.
8. And (3) a disinfection process:
the keys A, B, D, 2 are turned to ON, 1, X, to OFF, the rear pipeline of the desiccant bottle is disconnected, the Y-shaped tube 2 is connected, and the Y-shaped tube 2 is connected with the central temporary bottle 3 and the incubator 6.
The ozone generator 7 is started and ozone is delivered to the incubator 6. The first vacuum pump 5 pushes the ozone-containing gas in the incubator 6 to the central temporary bottle 3, and then sequentially passes through the large-diameter electromagnetic valve, the temperature and humidity monitoring box and the desiccant bottle, the Y-shaped pipe 2, and returns to the incubator 6, and the circulation is performed. The ozone generator 7 can set disinfection time, namely, timing disinfection, thereby realizing the timing disinfection function of the whole device.
In the present application, unless explicitly specified and limited otherwise, the terms "connected," "fixed," and the like are to be construed broadly and may be, for example, fixedly connected, detachably connected, or integrally formed; may be an electrical connection; can be directly connected or indirectly connected through an intermediate medium, and can be communicated with the inside of two elements or the interaction relationship of the two elements. The specific meaning of the above terms in the present application can be understood by those of ordinary skill in the art according to the specific circumstances.
In the description of the present application, numerous specific details are set forth. However, it is understood that embodiments of the application may be practiced without these specific details. In some instances, well-known methods, systems, and techniques have not been shown in detail in order not to obscure an understanding of this description.
In the description of the present specification, a description of the terms "one embodiment," "some embodiments," "examples," "particular examples," or "some examples," etc., means that a particular feature, system, material, or characteristic described in connection with the embodiment or example is included in at least one embodiment or example of the application. In this specification, schematic representations of the above terms are not necessarily directed to the same embodiment or example. Furthermore, the particular features, systems, materials, or characteristics may be combined in any suitable manner in any one or more embodiments or examples. Furthermore, the different embodiments or examples described in this specification and the features of the different embodiments or examples may be combined and combined by those skilled in the art without contradiction.
Finally, it should be noted that: the above embodiments are only for illustrating the technical solution of the present application, and not for limiting the same; although the application has been described in detail with reference to the foregoing embodiments, it will be understood by those of ordinary skill in the art that: the technical scheme described in the foregoing embodiments can be modified or some or all of the technical features thereof can be replaced by equivalents; such modifications and substitutions do not depart from the spirit of the application, and are intended to be included within the scope of the appended claims and description.

Claims (10)

1. The hard bronchoscope air pressure control jet ventilation auxiliary device is characterized by comprising a power supply module, a Y-shaped tube, a micro-pressure switch, an electromagnetic valve group and a central temporary bottle; one end of the Y-shaped tube is provided with two ventilation interfaces which are correspondingly connected with two side ports of the hard bronchoscope, and the other end of the Y-shaped tube is connected with a central temporary bottle; the electromagnetic valve group comprises a high-frequency electromagnetic valve group and a large-diameter electromagnetic valve; the high-frequency electromagnetic valve group is connected between the air source and the central temporary bottle; the large-diameter electromagnetic valve is connected between the central temporary bottle and the air inlet of the first air filter, and the air outlet of the first air filter is connected with the atmosphere; the micro-pressure switch is provided with a first pressure interface used for being connected with the injection pipeline and a second pressure interface used for being connected with the inclined port of the hard bronchoscope, is normally open and is connected between the output end of the power supply module and the input end of the electromagnetic valve group so as to control the electromagnetic valve group to be electrified or powered off;
when the jet ventilation and gas phase suction are performed, the micro-pressure switch is closed, the electromagnetic valve group is electrified to enable the gas source to be communicated with the central temporary bottle, and the first air filter is disconnected with the central temporary bottle;
when the jet ventilation breathes out the gaseous phase, the micro-pressure switch disconnection, solenoid valve group outage makes the air supply and central temporary bottle disconnection, and first air cleaner and central temporary bottle intercommunication.
2. The hard bronchoscope pneumatically controlled jet ventilation assist device of claim 1, further comprising a protective bottle, a second vacuum pump, CO 2 Detection port and O 2 The concentration detector, the inlet end of protection bottle is connected on the tie point of Y type pipe and central authorities' bottle of staying temporarily, the end of giving vent to anger of protection bottle is connected with the inlet end of second vacuum pump, and the end of giving vent to anger of second vacuum pump connects gradually CO 2 Detection port and O 2 The concentration detector is connected with a central temporary bottle.
3. The hard bronchoscope pneumatic control jet ventilation auxiliary device according to claim 1 or 2, wherein the air source comprises an oxygen source and an air source, the high-frequency electromagnetic valve group comprises an electromagnetic valve B and an electromagnetic valve C, the oxygen source is connected with a central temporary bottle through the electromagnetic valve B, and the air source is connected with a connecting point of the oxygen source and the electromagnetic valve B through the electromagnetic valve C.
4. The hard bronchoscope pneumatic control jet ventilation auxiliary device according to claim 3, wherein the second interface of the electromagnetic valve B is connected with an oxygen source, the first interface of the electromagnetic valve B is connected with a central temporary bottle, and the third interface of the electromagnetic valve B is connected with air; when the electromagnetic valve B is electrified, the second interface of the electromagnetic valve B is communicated with the first interface, and when the electromagnetic valve B is powered off, the second interface of the electromagnetic valve B is communicated with the third interface.
5. The hard bronchoscope air pressure control jet ventilation auxiliary device according to claim 4, wherein the air source is an incubator, an air inlet end of the incubator is communicated with the atmosphere through a second air filter, and an air outlet end of the incubator is connected with a second interface of the electromagnetic valve B through an electromagnetic valve C.
6. The hard bronchoscope pneumatic control jet ventilation auxiliary device according to claim 5, further comprising a first vacuum pump, wherein an air inlet end of the first vacuum pump is connected with an air outlet end of the incubator, the air outlet end of the first vacuum pump is connected with a second interface of an electromagnetic valve C, a first interface of the electromagnetic valve C is connected with a second interface of an electromagnetic valve B, and a third interface of the electromagnetic valve C is connected with the air inlet end of the incubator; when the electromagnetic valve C is electrified, the second interface is communicated with the first interface, and when the electromagnetic valve C is deenergized, the second interface is communicated with the third interface.
7. The hard bronchoscope air pressure control jet ventilation auxiliary device according to claim 5, further comprising an electromagnetic valve A and a humidifying bottle, wherein a second interface of the electromagnetic valve A is connected with an oxygen source, a first interface of the electromagnetic valve A is connected with an air inlet end of the humidifying bottle, and an air outlet end of the humidifying bottle and a third interface of the electromagnetic valve A are connected with a second interface of the electromagnetic valve B.
8. The hard bronchoscope pneumatic control jet ventilation auxiliary device according to claim 5, wherein a first interface of the large-diameter electromagnetic valve is connected with an outlet end of the incubator, a second interface of the large-diameter electromagnetic valve is connected with a central temporary bottle, and a third interface of the large-diameter electromagnetic valve is connected with the first air filter; when the large-diameter electromagnetic valve is electrified, the first interface is communicated with the second interface, and when the large-diameter electromagnetic valve is powered off, the second interface is communicated with the third interface.
9. The hard bronchoscope air pressure control jet ventilation auxiliary device according to claim 8, wherein a temperature and humidity detection box, an air drying agent and a flow sensor are sequentially connected between the third interface of the large-diameter electromagnetic valve and the first air filter.
10. The hard bronchoscope pneumatically controlled jet ventilation aid of claim 9, further comprising an ozone generator connected to the incubator.
CN202111073144.6A 2021-09-14 2021-09-14 Air pressure control jet ventilation auxiliary device for hard bronchoscope Active CN113730754B (en)

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CN204091925U (en) * 2014-09-01 2015-01-14 杭州市第一人民医院 The anti-infection face shield of a kind of breathing endoscope diagnosis and treatment
WO2021163946A1 (en) * 2020-02-20 2021-08-26 深圳迈瑞生物医疗电子股份有限公司 Medical ventilation device, control method, and computer readable storage medium
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