CN113730754A - Air pressure control jet ventilation auxiliary device for hard bronchoscope - Google Patents
Air pressure control jet ventilation auxiliary device for hard bronchoscope Download PDFInfo
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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
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- 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
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- 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
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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
- 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
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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
- 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
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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
- 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
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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
- A61M2205/00—General characteristics of the apparatus
- A61M2205/33—Controlling, regulating or measuring
- A61M2205/3368—Temperature
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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
- A61M2205/00—General characteristics of the apparatus
- A61M2205/75—General characteristics of the apparatus with filters
Abstract
The invention discloses an air pressure control jet ventilation auxiliary device for a hard bronchoscope, which comprises a power supply module, a Y-shaped tube, a micro-pressure switch, an electromagnetic valve group and a central temporary stay bottle, wherein the power supply module is connected with the Y-shaped tube; one end of the Y-shaped pipe is provided with a ventilation interface, and the other end of the Y-shaped pipe is connected with the central pivot temporary storage bottle; the electromagnetic valve group comprises a high-frequency electromagnetic valve group and a large-drift-diameter electromagnetic valve; the high-frequency electromagnetic valve group is connected between the air source and the central temporary staying bottle; the large-drift-diameter electromagnetic valve is connected between the central temporary staying bottle and an air inlet of the first air filter; the micro-pressure switch is provided with a first pressure interface and a second pressure interface, is in a normally open type, and is connected between the output end of the power supply module and the input end of the solenoid valve set so as to control the solenoid valve set to be powered on or powered off; airflow in the respiratory tract of the patient end enters the center temporary retention bottle and is output to the first air filter through the large-diameter electromagnetic valve to be filtered and then discharged, and the first air filter is arranged, so that the exhaled airflow of the patient can be filtered and then discharged, and air pollution can be effectively prevented.
Description
Technical Field
The invention relates to the technical field of medical instruments, in particular to an air pressure control jet ventilation auxiliary device for a hard bronchoscope.
Background
The hard bronchoscope is one of main tools of modern interventional pneumology, is matched with a bendable bronchoscope and other various instruments for use, and is a safe and effective interventional means for diagnosing and treating airway diseases. The specialized anesthesiologist can perform general anesthesia, diagnosis and treatment, and one of the key points is to ensure the safety and controllability of mechanical ventilation. Jet ventilation of a jet ventilation respirator is an efficient and convenient ventilation mode, and is favored by respiratory endoscopy doctors because the air passage openness is kept. The entrainment characteristic of the air flow around the jet orifice under the jet ventilation Venturi effect requires that the openness of the air passage is kept communicated with the atmosphere so as to ensure enough entrainment air volume. Due to the openness of the air passage, the expiratory phase gas of the patient is completely discharged into the air, and the patient is sprayed and ventilated downwards in an unknown disease diagnosis state, so that the air pollution of a consulting room is easily caused, and the exposure risk of medical staff involved in diagnosis and treatment is high. At present, the concentrations 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. For example, if the injection ventilation is performed for a long time, the respiratory mucosa is easy to dry, and complications such as hypothermia in the operation are easy to occur, the injection ventilation time needs to be strictly controlled, and the implementation of partial diagnosis and treatment is influenced.
Disclosure of Invention
Aiming at the defects in the prior art, the invention aims to provide a rigid bronchoscope air pressure control jet ventilation auxiliary device which can effectively prevent expiratory phase gas of a patient from being discharged into the air.
The technical scheme adopted by the invention is as follows:
the air pressure control jet ventilation auxiliary device for the hard bronchoscope comprises a power supply module, a Y-shaped tube, a micro-pressure switch, an electromagnetic valve group and a central temporary stay bottle; one end of the Y-shaped pipe 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 pipe is connected with the central temporary staying bottle; the electromagnetic valve group comprises a high-frequency electromagnetic valve group and a large-drift-diameter electromagnetic valve; the high-frequency electromagnetic valve group is connected between the air source and the central temporary staying bottle; the large-drift-diameter electromagnetic valve is connected between the central temporary staying bottle and an air inlet of a first air filter, and an 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 solenoid valve set so as to control the solenoid valve set to be powered on or powered off;
when the air is injected, ventilated and inhaled, the micro-pressure switch is closed, the solenoid valve group is electrified to enable the air source to be communicated with the central temporary storage bottle, and the first air filter is disconnected with the central temporary storage bottle;
when the jet ventilation and expiration phases occur, the micro-pressure switch is switched off, the electromagnetic valve group is switched off, so that the air source is disconnected from the central temporary storage bottle, and the first air filter is communicated with the central temporary storage bottle.
Further, the device also comprises a protective bottle, a second vacuum pump and CO2Detection port and O2The air inlet end of the protection bottle is connected to a connection point of the Y-shaped pipe and the central temporary storage bottle, the air outlet end of the protection bottle is connected with the air inlet end of a second vacuum pump, and the air outlet end of the second vacuum pump is sequentially connected with CO2Detection port and O2The concentration detector is connected with the central pivot temporary storage 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 storage bottle through the electromagnetic valve B, and the air source is connected to a connection 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 storage bottle, and a third interface of the electromagnetic valve B is connected with air; when the electromagnetic valve B is electrified, the second interface is communicated with the first interface, and when the electromagnetic valve B is powered off, the second interface is communicated with the third interface.
Further, the air source is a warm box, the air inlet end of the warm box is communicated with the atmosphere through a second air filter, and the air outlet end of the warm box is connected with the second interface of the electromagnetic valve B through an electromagnetic valve C.
The gas 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 gas 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 powered off, the second interface is communicated with the third interface.
The second interface of the electromagnetic valve A is connected with an oxygen source, the first interface of the electromagnetic valve A is connected with the air inlet end of the humidifying bottle, and the air outlet end of the humidifying bottle and the third interface of the electromagnetic valve A are both connected with the second interface of the electromagnetic valve B.
Furthermore, a first interface of the large-drift-diameter electromagnetic valve is connected with an air outlet end of the incubator, a second interface of the large-drift-diameter electromagnetic valve is connected with the central temporary staying bottle, and a third interface of the large-drift-diameter electromagnetic valve is connected with the first air filter; when the large-drift-diameter electromagnetic valve is electrified, the first interface is communicated with the second interface, and when the large-drift-diameter electromagnetic valve is powered off, the second interface is communicated with the third interface.
Furthermore, a temperature and humidity detection box, an air drying agent and a flow sensor are sequentially connected between a third interface of the large-drift-diameter electromagnetic valve and the first air filter.
Further, the ozone generator is also included and is connected with the incubator.
Additional aspects and advantages of the present 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 present application.
Drawings
In order to more clearly illustrate the detailed description of the invention or the technical solutions in the prior art, the drawings that are needed in the detailed description of the invention or the prior art will be briefly described below. Throughout the drawings, like elements or portions are generally identified by like reference numerals. In the drawings, elements or portions are not necessarily drawn to scale.
Fig. 1 is a schematic structural view of an air pressure control jet ventilation assisting device for a rigid bronchoscope according to an embodiment of the present disclosure;
FIG. 2 is an enlarged view of a portion of FIG. 1;
fig. 3 is a schematic structural diagram of a micro-pressure switch according to an embodiment of the present disclosure;
fig. 4 is a schematic circuit diagram of a micro-pressure switch connected to a solenoid valve set according to an embodiment of the present disclosure;
fig. 5 is a schematic view 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 bronchoscope 1, the Y-shaped tube 2, the central temporary stay 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, the O2Concentration detector 13, CO2The 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 drawings, the arrow direction represents the airflow direction.
Detailed Description
Embodiments of the present invention will be described in detail below with reference to the accompanying drawings. The following examples are only for illustrating the technical solutions of the present invention more clearly, and therefore are only examples, and the protection scope of the present invention is not limited thereby.
It is to be noted that, unless otherwise specified, technical or scientific terms used herein shall have the ordinary meaning as understood by those skilled in the art to which the invention pertains.
Referring to fig. 1 to 6, the pneumatic control jet ventilation auxiliary device for the rigid bronchoscope comprises a power module 18, a Y-shaped tube 2, a micro-pressure switch 19, a solenoid valve set and a central temporary stay bottle 3; one end of the Y-shaped pipe 2 is provided with two ventilation ports which are correspondingly connected with two side ports of the hard bronchoscope 1, and the other end of the Y-shaped pipe 2 is connected with the central temporary staying bottle 3; the electromagnetic valve group comprises a high-frequency electromagnetic valve group and a large-drift-diameter electromagnetic valve; the high-frequency electromagnetic valve group is connected between the air source and the central temporary staying bottle 3; the large-diameter electromagnetic valve is connected between the central temporary storage bottle 3 and an air inlet of the first air filter 10, and an 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 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 1, the micro-pressure switch 19 is in a normally open type, and is connected between the output end of the power supply module 18 and the input end of the solenoid valve set so as to control the solenoid valve set to be powered on or powered off; when the jet ventilation and suction phase occurs, the micro-pressure switch 19 is closed, the solenoid valve set is energized to connect the air source with the central dwell bottle 3 and disconnect the first air filter 10 from the central dwell bottle 3; when the jet ventilation phase is expired, the micro-pressure switch 19 is turned off, the solenoid valve set is de-energized to disconnect the air supply from the central dwell bottle 3 and the first air filter 10 is in communication with the central dwell bottle 3.
When the medical device is used, two ventilation interfaces of the Y-shaped tube 2 are respectively connected with two side ports of the hard bronchoscope 1, a first pressure interface of the micro-pressure switch 19 is connected with a jet ventilation respirator through a jet ventilation pipeline, and a second pressure interface of the micro-pressure switch 19 is connected with an oblique port of the hard bronchoscope 1; when the jet ventilation and inspiration phase is carried out, 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 effect, the electromagnetic valve group is electrified to enable the air source to be communicated with the central temporary stay bottle 3, so that the air is introduced into the central temporary stay bottle 3, when the jet airflow enters the hard bronchoscope 1, the Venturi effect is generated to suck the air in the central temporary stay bottle 3, and the ventilation efficiency can be greatly improved; when the jet ventilation and expiration phases are carried out, the micro-pressure switch 19 is restored to the disconnected state, the electromagnetic valve group is powered off to disconnect the air source from the central temporary storage bottle 3, air cannot enter the central temporary storage bottle 3, the first air filter 10 is communicated with the central temporary storage bottle 3 under the action of the large-diameter electromagnetic valve, air flow in a respiratory tract at the end of a patient enters the central temporary storage bottle 3 and is output to the first air filter 10 through the large-diameter electromagnetic valve to be filtered and then discharged, and through the arrangement of the first air filter 10, the air flow exhaled by the patient can be filtered and then discharged, so that air pollution can be effectively prevented.
In order to facilitate the detection of the exhaled gas, the device also comprises a protective bottle 16, a second vacuum pump 15, and CO2Detection ports 14 and O2An air inlet end of the protective bottle 16 is connected to a connection point of the Y-shaped pipe 2 and the central temporary holding bottle 3, an air outlet end of the protective bottle 16 is connected with an air inlet end of a second vacuum pump 15, and an air outlet end of the second vacuum pump 15 is sequentially connected with CO2Detection ports 14 and O2The concentration detector 13 is connected with the central temporary staying bottle 3.
The second vacuum pump 15 adopts a direct-current air pump of a miniature diaphragm pump, the model of which is EDLP600-D24B, the flow rate is 600ml/min, and the vacuum degree is 0.04 kpa. O is2The concentration detector 13 may be an intelligent portable oxygen meter ZY12C oxygen analyzer. By providing a second vacuum pump 15, a portion of the patient's exhaled air stream is directed into the central dwell bottle 3, and another small portion is passed through the CO by the second vacuum pump 152 Detection ports 14 and O2The concentration detectors 13 perform CO separation2Concentration and O2After the concentration is checked, the gas enters the central temporary staying bottle 3, and the CO of the air flow exhaled by the patient can be realized2Concentration and O2Concentration monitoring provides data support for anaesthetists to adjust the ventilation parameters of the jet breathing machine so as to accurately regulate and control the jet ventilation parameters
The micro-pressure switch 19 is an Isleke pressure difference switch with the pressure range of 500-2500 PA (engineering cost) and the pressure range of 500-2500 PA. The high-frequency electromagnetic valve group comprises two electromagnetic valves B and two electromagnetic valves C, wherein the two electromagnetic valves B are connected in parallel, the two electromagnetic valves C are connected in parallel, after the two electromagnetic valves B, the two electromagnetic valves C and the large-diameter electromagnetic valve are connected in parallel, the input end of the electromagnetic valve group is connected with one pole of the power module 18 through the micro-pressure switch 19, and the output end of the electromagnetic valve group is connected with the other pole of the power module 18. The micro-pressure switch 19 is normally open, when the micro-pressure switch 19 is disconnected, the electromagnetic valve group is powered off, and the second interface of the electromagnetic valve group is connected with the third interface; when the micro-pressure switch 19 is closed, the electromagnetic valve group is electrified, and the second interface of the electromagnetic valve group is connected with the first interface.
The air source comprises an oxygen source and an air source oxygen source which is connected with the central temporary storage bottle 3 through an electromagnetic valve B, and the air source is connected with the connection point of the oxygen source and the electromagnetic valve B through an 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 storage 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 storage 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.
Between air supply and solenoid valve B, still include solenoid valve A and humidification bottle 4, solenoid valve A's second interface is connected with the oxygen source, and solenoid valve A's first interface is connected with humidification bottle 4's inlet end, and humidification bottle 4's the third interface of giving vent to anger end and solenoid valve A all with solenoid valve B's second interface connection. 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 needs to be humidified, the second interface of the electromagnetic valve A is connected with the first interface, the oxygen output by the oxygen source is input into the humidifying bottle 4 through the second interface and the first interface of the electromagnetic valve A 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 a warm box 6, the air inlet end of the warm box 6 is communicated with the atmosphere through a second air filter 8, and the air outlet end of the warm box 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 electromagnetic valve B through the electromagnetic valve C, is mixed with oxygen, and then enters the central temporary storage bottle 3.
The incubator 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, the specification is 150 x 220mm, and the capacity is about 5L; the heater 9 heats the air in the oven 6 by blowing hot air into the oven 6. The heated gas enters the central dwell bottle 3 through solenoid valve C and solenoid valve B.
The humidifying bottle 4 and the heater 9 are arranged respectively, so that the gas introduced into the central temporary storage bottle 3 can be humidified and heated, the airway mucosa of a patient can be protected, and the normal body temperature can be maintained.
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 electromagnetic valve a, respectively, and the heater 9 and the electromagnetic valve a are controlled by the temperature and humidity controller 20 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 220 VAC. The temperature sensor and the humidity sensor are respectively used for detecting the temperature and the humidity of the gas and sending the detection result 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 result. 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 monitors that the temperature of the gas is lower than 30 ℃, the temperature and humidity controller 20 controls the PTC heater 9 to be started to heat the air, and if the temperature sensor monitors that the temperature of the gas is higher than 35 ℃, the temperature and humidity controller 20 controls the PTC heater 9 to stop heating; if the humidity sensor detects that the gas humidity is lower than 70 RH%, the second interface of the control electromagnetic valve A is connected with the first interface thereof, oxygen is guided into the humidifying bottle 4, and the gas is humidified by distilled water; if the humidity sensor detects that the humidity of the gas is higher than 95 RH%, the second interface of the control electromagnetic valve A is connected with the third interface thereof, so that oxygen is directly input into the electromagnetic valve B.
A first vacuum pump 5 is further arranged between the incubator 6 and the electromagnetic valve C, 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 is communicated with the first interface, and air in the incubator 6 enters the electromagnetic valve B through the second interface and the first interface of the electromagnetic valve C in sequence under the action of the first vacuum pump 5 to provide air required by respiration 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 through the second interface and the third interface of the electromagnetic valve C under the action of the first vacuum pump 5.
The model of the first vacuum pump 5 is VN-C1/24V, the flow rate is 15L/min, the power is 10w, and the vacuum degree is-80 kpa.
The model of the large-drift-diameter electromagnetic valve D is DVG342R-5G-10, 1 inch, and the drift diameter area is 210-235 mm2Converted into a circle, the inner diameter D is approximately equal to 16.36 mm-17.30 mm, DC 24V. A first interface of the large-drift-diameter electromagnetic valve D is connected with an air outlet end of the incubator 6, a second interface of the large-drift-diameter electromagnetic valve is connected with the central temporary storage bottle 3, and a third interface of the large-drift-diameter electromagnetic valve is connected with the first air filter 10; when the large-drift-diameter electromagnetic valve is electrified, the first interface is communicated with the second interface, and air in the incubator 6 is guided into the central temporary storage bottle 3; when the large-drift-diameter electromagnetic valve is powered off, the second interface is communicated with the third interface, and the airflow in the central temporary storage bottle 3 is guided out to the first air filter 10 to be filtered and then 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 of the temperature and humidity controller 20 are arranged in the temperature and humidity detection box 12 and used for detecting the temperature and the humidity of the exhaled air flow and sending a monitoring result to the temperature and humidity controller 20, and the temperature and the humidity of the inhaled air are adjusted by the temperature and humidity controller 20 through controlling the on-off electricity of the electromagnetic valve A and the heater. The air desiccant bottle 11 has a capacity of about 250ml and acts to dry the air flowing through it to ensure proper use of the flow controller. The flow sensor 17 adopts an MF4000 series microminiature gas flow controller, and the specification of the flow sensor is MF 4008-10L/min.
In order to disinfect the pipeline through which the exhaled air flows, the ozone generator 7 is further included, and the ozone generator 7 is connected with the air inlet end of the incubator 6.
After the use of one case is finished, a 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 pipeline between the Y-shaped pipe 2, the central temporary staying bottle 3, the large-diameter electromagnetic valve D, the temperature and humidity detection box 12 and the air drying agent bottle 11, a protective bottle 16, a second vacuum pump 15, CO2Detection ports 14 and O2The pipelines between the concentration detectors 13 are 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 exhaled air flows are automatically disinfected to prevent cross infection.
Furthermore, the micro-pressure switch 19 can be manually controlled to electrify the electromagnetic valve B, the electromagnetic valve C and the large-diameter electromagnetic valve D, and the pipelines between 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 that the pipelines through which air flows are disinfected, and cross infection is further prevented.
The electromagnetic valve B and the electromagnetic valve C can adopt a two-position three-way electromagnetic valve with the model number of VT307-5G-02, and the working voltage is 220 VAC.
In practical applications, several switches, such as A, B, C, D, 1, 2, X, may be provided. A: a power supply 24VDC controls a large-diameter electromagnetic valve D, an electromagnetic valve B1, an electromagnetic valve B2, an electromagnetic valve C1 and an electromagnetic valve C2; b: a power supply 24VDC controlling the first vacuum pump 5 and the second vacuum pump 15; c: a power supply 220VAC, a temperature and humidity control instrument → a PTC heater 9 and a 220VAC high-frequency electromagnetic valve; d: a power supply 220VAC for controlling the ozone generator 7; 1. the large-drift-diameter electromagnetic valve D can be independently controlled to be switched on and off; 2. the micro-pressure switch 19 can be controlled to be artificially short-circuited; x: the second vacuum pump 15 can be controlled to be switched on and off.
The working process is as follows:
1. the power supply of the whole machine is switched on, the flow sensor 17 is preheated for about 10min, and the whole machine is connected with wall type oxygen, wall type air and an injection pipeline (the inner diameter is 5mm, and the outer diameter is 8mm) of an injection ventilation respirator;
2. keys A, B, 1, X are pressed to the ON position, and the rest are in the OFF state;
3. the injection ventilation is started, the air pressure of the air suction phase injection pipeline is quickly increased to drive the micro-pressure switch 19 to be in short circuit, and the large-drift-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, the warm air passes through the high-frequency electromagnetic valve groups C1 and C2, is mixed with humidified/unhumidified oxygen and then is pushed to the central temporary storage bottle 3;
5. the jet air flow is jetted from the outlet of the hard mirror jet joint, air around the jet orifice is sucked by entrainment under the action of Venturi effect, and the warm mixed gas in the central temporary staying bottle 3 is pushed to the hard bronchoscope under the action of atmospheric pressure;
6. when the injection, ventilation and air suction phase is finished, the micro-pressure switch 19 is switched off, and the large-path electromagnetic valve and the high-frequency electromagnetic valve banks C1 and C2 are closed; under the comprehensive action of respiratory muscles such as intercostal muscles of the thorax, diaphragm muscles and the like, the lung elastically retracts, and gas in the respiratory tract is exhaled, flows through the central temporary storage bottle 3, the large-drift-diameter electromagnetic valve, the temperature and humidity detection box 12, the air drying agent bottle 11 and the flow sensor 17 in sequence, and is finally discharged into a special waste gas pipeline in the consulting room after being treated by the air filter;
7. inhalation phase + exhalation phase, the second vacuum pump 15 is continuously operating. A suction port of a second vacuum pump 15, air outlets of which are all positioned in the central temporary holding bottle 3, an air outlet pipeline is connected with a protective bottle 16, and the pipeline can be connected with a PETCO2 sampling pipe to monitor PETCO2 (end-tidal carbon dioxide); in addition, the gas outlet pipeline is connected with an intelligent portable oxygen meter ZY12C oxygen analyzer for monitoring the concentration change of O2.
8. And (3) disinfection process:
keys A, B, D, 2 are turned to ON state, 1, X, and OFF state, the pipeline behind the desiccant bottle is disconnected, and is connected with Y-shaped pipe 2, and Y-shaped pipe 2 is connected with central temporary holding bottle 3 and incubator 6.
The ozone generator 7 is started and ozone is delivered to the incubator 6. The first vacuum pump 5 pushes the gas containing ozone in the incubator 6 to the central temporary storage bottle 3, and then the gas returns to the incubator 6 through the large-path electromagnetic valve, the temperature and humidity monitoring box, the drying agent bottle and the Y-shaped pipe 2 in sequence, and the process is repeated. The ozone generator 7 can set the disinfection time, namely regularly disinfect, thereby realizing the regular disinfection function of the whole device.
In this application, unless expressly stated or limited otherwise, the terms "connected," "secured," and the like are to be construed broadly and can include, for example, fixed connections, removable connections, or integral combinations thereof; may be an electrical connection; either directly or indirectly through intervening media, either internally or in any other relationship. The specific meanings of the above terms in the present invention can be understood by those skilled in the art according to specific situations.
In the description of the present invention, numerous specific details are set forth. It is understood, however, that embodiments of the invention 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 herein, references to the description of the term "one embodiment," "some embodiments," "an example," "a specific example," or "some examples," etc., mean 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 invention. In this specification, the schematic representations of the terms used above are not necessarily intended to refer to the same embodiment or example. Furthermore, the particular features, systems, materials, or characteristics described may be combined in any suitable manner in any one or more embodiments or examples. Furthermore, various embodiments or examples and features of different embodiments or examples described in this specification can be combined and combined by one skilled in the art without contradiction.
Finally, it should be noted that: the above embodiments are only used to illustrate the technical solution of the present invention, and not to limit the same; while the invention has been described in detail and with reference to the foregoing embodiments, it will be understood by those skilled in the art that: the technical solutions described in the foregoing embodiments may still be modified, or some or all of the technical features may be equivalently replaced; such modifications and substitutions do not depart from the spirit and scope of the present invention, and they should be construed as being included in the following claims and description.
Claims (10)
1. The air pressure control jet ventilation auxiliary device for the hard bronchoscope is characterized by comprising a power supply module, a Y-shaped tube, a micro-pressure switch, an electromagnetic valve group and a central temporary stay bottle; one end of the Y-shaped pipe 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 pipe is connected with the central temporary staying bottle; the electromagnetic valve group comprises a high-frequency electromagnetic valve group and a large-drift-diameter electromagnetic valve; the high-frequency electromagnetic valve group is connected between the air source and the central temporary staying bottle; the large-drift-diameter electromagnetic valve is connected between the central temporary staying bottle and an air inlet of a first air filter, and an 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 solenoid valve set so as to control the solenoid valve set to be powered on or powered off;
when the air is injected, ventilated and inhaled, the micro-pressure switch is closed, the solenoid valve group is electrified to enable the air source to be communicated with the central temporary storage bottle, and the first air filter is disconnected with the central temporary storage bottle;
when the jet ventilation and expiration phases occur, the micro-pressure switch is switched off, the electromagnetic valve group is switched off, so that the air source is disconnected from the central temporary storage bottle, and the first air filter is communicated with the central temporary storage bottle.
2. The rigid bronchoscope air pressure controlled jet ventilation aid of claim 1, further comprising a protective bottle, a second vacuum pump, CO2Detection port and O2The air inlet end of the protection bottle is connected to a connection point of the Y-shaped pipe and the central temporary storage bottle, the air outlet end of the protection bottle is connected with the air inlet end of a second vacuum pump, and the second vacuum pumpThe air outlet end of the gas pipe is connected with CO in sequence2Detection port and O2The concentration detector is connected with the central pivot temporary storage bottle.
3. The rigid bronchoscope air pressure control jet ventilation aid of claim 1 or 2, wherein the air source comprises an oxygen source and an air source, the high frequency solenoid valve set comprises a solenoid valve B and a solenoid valve C, the oxygen source is connected with the central dwell bottle through the solenoid valve B, and the air source is connected with a connection point of the oxygen source and the solenoid valve B through the solenoid valve C.
4. The rigid bronchoscope air pressure control jet ventilation aid of claim 3, wherein the second port of solenoid valve B is connected to an oxygen source, the first port of solenoid valve B is connected to a central dwell bottle, and the third port of solenoid valve B is connected to air; when the electromagnetic valve B is electrified, the second interface is communicated with the first interface, and when the electromagnetic valve B is powered off, the second interface is communicated with the third interface.
5. The rigid bronchoscope air pressure control jet ventilation aid 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 solenoid valve B through a solenoid valve C.
6. The pneumatic control jet ventilation auxiliary device for the hard bronchoscope according to claim 5, further comprising a first vacuum pump, an air inlet of which is connected to an air outlet of the incubator, an air outlet of which is connected to a second port of a solenoid valve C, a first port of which is connected to a second port of a solenoid valve B, and a third port of which is connected to an air inlet 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 powered off, the second interface is communicated with the third interface.
7. The rigid bronchoscope air pressure control jet ventilation auxiliary device according to claim 5, further comprising a solenoid valve A and a humidification bottle, wherein the second port of the solenoid valve A is connected with an oxygen source, the first port of the solenoid valve A is connected with the air inlet end of the humidification bottle, and the air outlet end of the humidification bottle and the third port of the solenoid valve A are both connected with the second port of the solenoid valve B.
8. The rigid bronchoscope air pressure control jet ventilation assisting device according to claim 5, wherein a first interface of the large-drift-diameter solenoid valve is connected with an air outlet end of an incubator, a second interface of the large-drift-diameter solenoid valve is connected with a central temporary staying bottle, and a third interface of the large-drift-diameter solenoid valve is connected with a first air filter; when the large-drift-diameter electromagnetic valve is electrified, the first interface is communicated with the second interface, and when the large-drift-diameter electromagnetic valve is powered off, the second interface is communicated with the third interface.
9. The pneumatic control jet ventilation auxiliary device for the hard bronchoscope 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 solenoid valve and the first air filter.
10. The rigid bronchoscope air pressure controlled jet ventilation aid of claim 9, further comprising an ozone generator connected to the incubator.
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