CN114432559A - Air duct with stable pressure difference and connecting device - Google Patents
Air duct with stable pressure difference and connecting device Download PDFInfo
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- CN114432559A CN114432559A CN202210117334.1A CN202210117334A CN114432559A CN 114432559 A CN114432559 A CN 114432559A CN 202210117334 A CN202210117334 A CN 202210117334A CN 114432559 A CN114432559 A CN 114432559A
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- 238000005399 mechanical ventilation Methods 0.000 claims abstract description 83
- 238000009423 ventilation Methods 0.000 claims abstract description 51
- 238000007789 sealing Methods 0.000 claims abstract description 43
- 230000029058 respiratory gaseous exchange Effects 0.000 claims description 87
- 230000000087 stabilizing effect Effects 0.000 claims description 55
- 239000012528 membrane Substances 0.000 claims description 11
- 230000006698 induction Effects 0.000 claims description 3
- 210000004877 mucosa Anatomy 0.000 abstract description 24
- 230000017531 blood circulation Effects 0.000 abstract description 8
- 230000006378 damage Effects 0.000 abstract description 6
- 239000007789 gas Substances 0.000 description 110
- 230000006641 stabilisation Effects 0.000 description 17
- 238000011105 stabilization Methods 0.000 description 17
- 239000013589 supplement Substances 0.000 description 13
- 210000004379 membrane Anatomy 0.000 description 9
- 230000000241 respiratory effect Effects 0.000 description 8
- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 description 7
- 230000003434 inspiratory effect Effects 0.000 description 7
- 239000001301 oxygen Substances 0.000 description 7
- 229910052760 oxygen Inorganic materials 0.000 description 7
- 238000003825 pressing Methods 0.000 description 7
- 230000006835 compression Effects 0.000 description 6
- 238000007906 compression Methods 0.000 description 6
- 238000000034 method Methods 0.000 description 6
- 210000003437 trachea Anatomy 0.000 description 5
- 206010002091 Anaesthesia Diseases 0.000 description 4
- 230000037005 anaesthesia Effects 0.000 description 4
- 230000034994 death Effects 0.000 description 4
- 230000000302 ischemic effect Effects 0.000 description 4
- 210000004072 lung Anatomy 0.000 description 4
- 230000017074 necrotic cell death Effects 0.000 description 4
- 210000004712 air sac Anatomy 0.000 description 3
- 238000010276 construction Methods 0.000 description 3
- 239000002775 capsule Substances 0.000 description 2
- 208000015181 infectious disease Diseases 0.000 description 2
- 208000028867 ischemia Diseases 0.000 description 2
- 238000012544 monitoring process Methods 0.000 description 2
- 238000002640 oxygen therapy Methods 0.000 description 2
- 238000006213 oxygenation reaction Methods 0.000 description 2
- 238000005086 pumping Methods 0.000 description 2
- 231100000241 scar Toxicity 0.000 description 2
- 230000002269 spontaneous effect Effects 0.000 description 2
- 238000002627 tracheal intubation Methods 0.000 description 2
- 206010011224 Cough Diseases 0.000 description 1
- 206010014568 Empyema Diseases 0.000 description 1
- 206010016717 Fistula Diseases 0.000 description 1
- 206010021143 Hypoxia Diseases 0.000 description 1
- 208000032376 Lung infection Diseases 0.000 description 1
- 208000031481 Pathologic Constriction Diseases 0.000 description 1
- 206010057190 Respiratory tract infections Diseases 0.000 description 1
- 206010049418 Sudden Cardiac Death Diseases 0.000 description 1
- 206010044310 Tracheo-oesophageal fistula Diseases 0.000 description 1
- 208000005864 Tracheoesophageal Fistula Diseases 0.000 description 1
- 208000027418 Wounds and injury Diseases 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 230000036770 blood supply Effects 0.000 description 1
- 210000000621 bronchi Anatomy 0.000 description 1
- 238000006243 chemical reaction Methods 0.000 description 1
- 210000000038 chest Anatomy 0.000 description 1
- 230000007423 decrease Effects 0.000 description 1
- 230000007547 defect Effects 0.000 description 1
- 238000007599 discharging Methods 0.000 description 1
- 230000009977 dual effect Effects 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 239000000284 extract Substances 0.000 description 1
- 230000003890 fistula Effects 0.000 description 1
- 238000002695 general anesthesia Methods 0.000 description 1
- 208000018875 hypoxemia Diseases 0.000 description 1
- 208000014674 injury Diseases 0.000 description 1
- 208000037906 ischaemic injury Diseases 0.000 description 1
- 208000016274 isolated tracheo-esophageal fistula Diseases 0.000 description 1
- 238000012423 maintenance Methods 0.000 description 1
- 238000004519 manufacturing process Methods 0.000 description 1
- 210000004400 mucous membrane Anatomy 0.000 description 1
- 201000003144 pneumothorax Diseases 0.000 description 1
- 230000002685 pulmonary effect Effects 0.000 description 1
- 238000011084 recovery Methods 0.000 description 1
- 210000002345 respiratory system Anatomy 0.000 description 1
- 230000036262 stenosis Effects 0.000 description 1
- 208000037804 stenosis Diseases 0.000 description 1
- 208000014221 sudden cardiac arrest Diseases 0.000 description 1
- 210000000115 thoracic cavity Anatomy 0.000 description 1
- 210000000779 thoracic wall Anatomy 0.000 description 1
- 208000006601 tracheal stenosis Diseases 0.000 description 1
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Classifications
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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
- A61M16/04—Tracheal tubes
- A61M16/0434—Cuffs
- A61M16/044—External cuff pressure control or supply, e.g. synchronisation with respiration
-
- 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
- A61M16/20—Valves specially adapted to medical respiratory devices
- A61M16/208—Non-controlled one-way valves, e.g. exhalation, check, pop-off non-rebreathing valves
-
- 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
-
- 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
- A61M2205/3379—Masses, volumes, levels of fluids in reservoirs, flow rates
Abstract
The invention discloses a pressure difference stable vent pipe and a connecting device, belonging to the field of medical instruments, comprising a vent pipe body, wherein the front section of the vent pipe body is provided with a sealing air bag; the pressure of the ventilation catheter sealing air bag is synchronously and dynamically changed along with the airway pressure of mechanical ventilation, and in an expiratory phase with smaller mechanical ventilation airway pressure, the air pressure in the sealing air bag is smaller, the blood circulation of tracheal mucosa is recovered, and the damage to the tracheal mucosa is avoided.
Description
Technical Field
The invention relates to the field of medical treatment, in particular to the field of medical catheters.
Background
General anesthesia or ICU patients need to put the tracheal catheter into the trachea through mouth or nose, and then the anesthesia machine or the respirator assists breathing. The sealed capsule body has long pressing time on the tracheal mucosa, can cause slight ischemic necrosis at the pressing part of the tracheal mucosa, is easy to cause respiratory tract infection and cough of a patient, even develops pulmonary infection, and is extremely unfavorable for the recovery of the patient; various serious complications may develop at the site of tracheal mucosal compression: for example, tracheoesophageal fistula seriously affects the life safety of patients, and the fatality rate is about 50 percent; the tracheal mucosa scar is formed to cause tracheal stenosis, the scar is gradually proliferated, the stenosis is gradually aggravated, even the ventilation of a patient is influenced, the tracheal stent needs to be placed in, but only the patient is palliatively treated, and the patient is difficult to escape from death; thirdly, the tracheal thoracic fistula causes tension pneumothorax, and if the death rate is not timely cured, the death rate is extremely high; fourthly, the lung infection, even the thorax infection, causes empyema, and the treatment is very troublesome.
In order to reduce the incidence of the above complications, the current clinical common methods are: firstly, when the air is filled into the tracheal catheter sealing bag body, the operation is accurate, the pressure meter is used for filling air, the filling pressure is generally 30mmHg, but the filling pressure needs to be properly increased for patients with poor lung compliance. The method avoids overhigh inflation pressure of the air bag, reduces the compression of the sealed air bag on the tracheal mucosa as much as possible, prolongs the compression-resistant time of the compressed part of the tracheal mucosa, and still avoids the consequences of ischemic necrosis for patients with long mechanical ventilation; secondly, mechanically ventilating the patient in the trachea cannula, and periodically evacuating the gas in the sealing air bag to recover the blood circulation of the airway mucosa for a short time. The method needs more manual intervention, wastes time and labor, and meanwhile, when the air in the sealed air bag is pumped out, the mechanical ventilation and air leakage are serious, the ventilation effect of a patient is seriously influenced, the oxygenation of the patient is influenced, and even the patient is lack of oxygen. If the operation is wrong, the air is not supplemented into the sealed air bag in time, and extremely serious complications, such as hypoxemia, sudden cardiac arrest and even death, are caused. And thirdly, the double-sealed-bag tracheal catheter is used for the patient who is mechanically ventilated in the tracheal intubation, the pressing position of the sealed air bags is periodically and alternately replaced, the tracheal mucosa part pressed by the air bags is periodically alternated between the two sealed air bags, and the tracheal mucosa part pressed by the air bags is periodically recovered. This method also requires a lot of manual intervention, which is time consuming and laborious. When the operation is not proper: for example, the pressure of the gas filled in the air bags is too high, the intermittent time of alternate inflation is too long, the operation is forgotten, and the like, so that the compression parts of the two sealed air bags are subjected to ischemic necrosis, and the occurrence rate of double complications is caused. Even if the management is completely in place, in some patients with poor tolerance, the tracheal mucosa blood circulation is still seriously affected due to the filling of 30mmHg pressure, and the ischemic necrosis still occurs.
One proposed solution is that in application No. 202210080092.3, the tracheal catheter sealing air bag can avoid pressure injury to airway mucosa; however, when the pressure of the hyperbaric oxygen chamber is increased or reduced for the oxygen therapy of the patient in the original scheme, a proper amount of gas needs to be filled into or discharged from the sealing air bag in time, and medical care personnel needs to operate the sealing air bag in time, otherwise serious mechanical ventilation and air leakage or serious compression of mucosa in the airway of the patient can be caused, and even more serious complications can be caused by carelessness.
We think and verify further on the original basis and propose a new solution. The safety of the scheme is higher, and when the hyperbaric oxygen chamber of the patient is used for oxygen therapy, the sealing air bag is not required to be filled or exhausted additionally, the mechanical ventilation sealing performance can be ensured under any condition, and the damage to the inner wall of the mucosa of the airway can be avoided.
Disclosure of Invention
Aiming at the defects in the prior art, the airway tube with stable pressure difference comprises an airway tube body, wherein a sealing air bag is arranged at the head section of the airway tube body, and a pressure difference stabilizing cavity is communicated with the sealing air bag. The pressure difference stabilizing cavity is communicated with an air charging device and a one-way pressure overflow exhaust valve. The inflation device is provided with an air inlet and an air outlet. The gas outlet is communicated with the pressure difference stabilizing cavity, gas can be filled into the pressure difference stabilizing cavity through the inflating device, the overflow exhaust valve is provided with a gas inlet and a gas outlet, the inner cavity of the overflow exhaust valve is provided with an overflow valve and an overflow valve opening which are matched, and the overflow valve is in stressed movable contact with the overflow valve opening on one side close to the gas outlet. The air inlet is communicated with the pressure difference stabilizing cavity, the overflow valve is in contact with the air in the breathing loop during mechanical ventilation at one side of the air outlet, and the overflow air in the pressure difference stabilizing cavity can be discharged through the overflow exhaust valve.
A connecting device with stable pressure difference comprises a pressure difference stabilizing cavity, wherein an inflating device and a one-way pressure overflow exhaust valve are communicated with the pressure difference stabilizing cavity. The air charging device is provided with an air inlet and an air outlet, the air outlet is communicated with the pressure difference stabilizing cavity, and air can be charged into the pressure difference stabilizing cavity through the air charging device. The overflow pressure exhaust valve is provided with an air inlet and an air outlet, the inner cavity of the overflow pressure exhaust valve is provided with an overflow pressure valve and an overflow pressure valve opening which are matched, and the overflow pressure valve is in stressed movable contact with the overflow pressure valve opening at one side close to the air outlet. The air inlet is communicated with the pressure difference stabilizing cavity, the pressure overflow valve is in contact with the air in the breathing loop during mechanical ventilation at one side of the air outlet, and the pressure overflow air in the pressure difference stabilizing cavity can be discharged through the pressure overflow exhaust valve. The pressure difference stabilizing cavity is communicated with an inflation fixing interface matched with an inflation port of the ventilation catheter and is provided with a respiration connecting pipe matched with a respiration loop.
Further, the air inlet of the inflation device is communicated with the mechanical ventilation breathing loop, the air outlet of the pressure overflow exhaust valve is communicated with the mechanical ventilation breathing loop, the inflation device sucks air from the mechanical ventilation breathing loop and fills the pressure difference stabilizing cavity, and the pressure overflow gas in the pressure difference stabilizing cavity is exhausted to the mechanical ventilation breathing loop through the pressure overflow exhaust valve.
Further, the air inlet of the air charging device is communicated with the outside, and the air outlet of the overflow exhaust valve is communicated with the outside. The pressure overflow valve of the pressure overflow exhaust valve is communicated with the mechanical ventilation breathing loop in a sealing way to be provided with a pressure induction soft film bag, and the exhaust port is arranged outside the cavity of the soft film bag.
Further, the overflow exhaust valve comprises an electromagnetic exhaust valve or a spring exhaust valve, and the exhaust threshold of the overflow exhaust valve can be adjusted by adjusting the deformation amplitude of the resistor or the spring.
Furthermore, the mechanical ventilation breathing circuit comprises a ventilation catheter tube body and a breathing connecting tube, wherein two ends of the breathing connecting tube are respectively matched with the ventilation catheter tube body and the breathing threaded tube.
Go toStep (b), the exhaust threshold value P of the overflow exhaust valve5For stabilizing the gas pressure P in the chamber by differential pressure3With the pressure P of the gas in the mechanical ventilation breathing circuitAirwayThe difference between them. When (P)3-PAirway)＞P5When the pressure-relief valve leaves the pressure-relief valve opening, the gas in the pressure-difference stabilization cavity is exhausted through the pressure-relief exhaust valve. When (P)3-PAirway)＜P5When the pressure relief valve is used, the pressure relief valve blocks the pressure relief valve opening, and the gas in the pressure difference stabilization cavity cannot be discharged through the pressure relief exhaust valve.
Further, the exhaust threshold value P of the overflow exhaust valve (5)5＜15mmHg。
Further, a gas pressure sensor is arranged in the air bag or the air bag communicated with the air catheter body, and the gas pressure P in the air bag or the air bag is monitored and displayed2. A gas pressure sensor is arranged in the mechanical ventilation and respiration loop and is communicated with the mechanical ventilation and respiration loop to monitor and display the gas pressure P in the mechanical ventilation and respiration loopAirway。
Furthermore, the pressure difference stabilizing cavity is communicated with the sealed air bag through an inflation tube, the inflation tube is provided with a switch, and one side of the inflation tube close to the sealed air bag is provided with a pressure valve inflation inlet.
The invention has the beneficial effects that:
1. during mechanical ventilation, the inspiratory phase time is short, and the expiratory phase time is long (generally 1: 2). Meanwhile, the pressure of an inspiratory phase airway is higher (generally not more than 25mmHg), and the pressure of an expiratory phase is lower (generally not more than 5 mmHg); when the device is in a long expiration phase, the pressure of the sealing air bag is low, the blood circulation of the tracheal mucosa at the pressing part of the sealing air bag is hardly influenced, and ischemia of the tracheal mucosa can be avoided;
2. when the hyperbaric oxygen chamber is used for treating pressurization or depressurization, the pressure of the sealing air bag can be automatically adjusted along with the pressure of the air passage without inflating and deflating the air bag, so that the sealing performance during mechanical ventilation is ensured, the sealing air bag is prevented from pressing the mucosa of the air passage too strongly, and the oxygenation safety of a patient is ensured;
3. need not too much manual intervention operation, avoid forgetting, only need open the pump when initial can, need not to set up.
Drawings
FIG. 1 is a sectional view showing the structure of a first embodiment of the present invention;
FIG. 2 is a sectional view showing the structure of a second embodiment of the present invention;
FIG. 3 is a sectional view showing the construction of a third embodiment of the present invention;
FIG. 4 is a sectional view showing the construction of a fourth embodiment of the present invention;
FIG. 5 is a cross-sectional view illustrating a fifth embodiment of the present invention;
FIG. 6 is a sectional view showing the construction of a sixth embodiment of the present invention;
FIG. 7 is a schematic view of the overpressure gas escape path of FIGS. 1, 3 and 5 in accordance with the present invention;
FIG. 8 is a schematic illustration of the overpressure gas escape path of FIGS. 2, 4 and 6 in accordance with the present invention;
FIG. 9 is P during PCV mode mechanical ventilation according to the present invention2And PAirwayPressure time axis plot.
FIG. 10 shows P during mechanical ventilation in VCV mode according to the present invention2And PAirwayPressure time axis plot. Number and name:
1-an air duct body, 2-a sealed air bag, 3-a differential pressure stable cavity, 4-an inflating device, 41-an air inlet, 42-an air outlet, 5-an overflow exhaust valve, 51-an air inlet, 52-an air outlet, 53-an overflow valve, 54-an overflow valve opening, 55-a soft membrane bag, 6-an inflating fixed interface, 7-a breathing connecting pipe, 8-an inflating pipe, 81-a switch and 82-a pressure valve inflating opening.
Detailed Description
In order to make the technical solutions of the present invention better understood and make the above features, objects, and advantages of the present invention more comprehensible, the present invention is further described below with reference to the following examples. The examples are intended to illustrate the invention only and are not intended to limit the scope of the invention.
1-4, a pressure differential stable airway tube and connection device includes an airway tube body 1, the airway tube body 1 including various types of endotracheal tube body tubes, such as single lumen endotracheal tubes, dual lumen endotracheal tubes, bronchial occluders, tracheostomy tubes, and the like. When the mechanical ventilation is performed, the head section of the ventilation catheter tube body 1 is reserved in the airway cavity of a patient, the head section of the ventilation catheter tube body 1 is provided with the sealing air bag 2, the sealing air bag 2 is filled with a proper amount of gas, the pressure intensity of the sealing air bag 2 is larger than the air pressure of the airway, and the sealing air bag 2 is in full contact with the mucosa in the airway cavity, so that ventilation sealing performance is provided for the mechanical ventilation. These basic structures are substantially similar to existing airway tubes and will not be described in detail herein.
During mechanical ventilation, the inspiratory phase time is short, and the expiratory phase time is long (generally 1: 2). Meanwhile, the inspiratory pressure of the airway is higher, and the expiratory pressure is lower. The purpose of the invention is: in the expiratory phase with longer time occupation and lower airway pressure, the gas capacity in the sealed air bag 2 is adjusted to ensure that the gas pressure in the sealed air bag 2 is lower, thereby reducing the pressure of the sealed air bag 2 to airway mucosa. The tracheal mucosa at the pressing part of the sealed air bag 2 occupies a longer expiration phase and has lower pressure, the blood circulation is recovered, and the blood circulation which almost occupies 2/3 ventilation time is basically not influenced, so that the ischemia of the tracheal mucosa is avoided.
In order to achieve the design goal, the invention is communicated with the sealing air bag 2 to be provided with a differential pressure stabilizing cavity 3, and the function is to keep the gas pressure of the sealing air bag 2 and the gas pressure in the breathing loop in non-isobaric balance during mechanical ventilation. That is, the gas pressure of the sealed air bag 2 is made to be higher than the gas pressure in the breathing circuit, and the difference between the gas pressure of the sealed air bag 2 and the gas pressure in the breathing circuit is a stable value which is controlled to be between 2 and 10mmHg, and 5mmHg is optimal. The pressure of the expiratory phase is lower, about 1mmHg, when most patients are ventilated mechanically; the pressure during the inspiratory phase is high, about 15 mmHg. By controlling the difference between the air pressure of the sealing air bag 2 and the air pressure in the breathing circuit to be 5mmHg, the air pressure of the sealing air bag 2 (namely the pressure of the sealing air bag 2 to the mucous membrane on the inner wall of the airway) can be controlled to fluctuate between 6 and 20 mmHg. The expiration phase which occupies a longer time is lower and is about 6mmHg, so that the blood circulation of the mucosa on the inner wall of the airway pressed by the sealing air bag 2 is hardly influenced during the expiration phase, and the ischemic injury is completely avoided.
In order to achieve the above purpose, as shown in fig. 1-4, a pressure difference stabilizing chamber 3 is arranged to communicate with the sealed air bag 2, and an inflating device 4 and a one-way overflow exhaust valve 5 are arranged to communicate with the pressure difference stabilizing chamber 3. The air charging device 4 continuously charges air into the differential pressure stabilizing cavity 3, and exhausts overpressure air through the one-way pressure overflow exhaust valve 5, so that the pressure intensity of the differential pressure stabilizing cavity 3 is greater than the air pressure of the air passage, and the difference value is the pressure relief threshold value P of the one-way pressure overflow exhaust valve 55. The pressure difference stabilizing cavity 3 is communicated with the sealed air bag 2, and the dynamic equal balance of the gas pressure of the pressure difference stabilizing cavity 3 and the sealed air bag 2 is realized; therefore, the pressure of the sealing air bag 2 is higher than the air pressure of the air passage.
The one-way overflow exhaust valve 5 is provided with an air inlet 51 and an air outlet 52, the air inlet 51 is communicated with the differential pressure stabilization cavity 3, the inner cavity of the overflow exhaust valve 5 is provided with an overflow valve 53 and an overflow valve opening 54 which are matched, and the overflow valve 53 is in stressed movable contact with the overflow valve opening 54 at one side close to the air outlet 52. The pressure overflow valve 53 is in contact with the gas in the breathing circuit during mechanical ventilation at one side of the exhaust port 52, and the pressure overflow gas in the pressure difference stabilization cavity 3 can be exhausted through the pressure overflow exhaust valve 5.
The air inlet 51 of the one-way overflow exhaust valve 5 is communicated with the differential pressure stabilization cavity 3, the overflow valve 53 is contacted with the gas in the breathing circuit during mechanical ventilation at one side of the exhaust port 52, so that the gas pressure of the differential pressure stabilization cavity 3 is related with the gas pressure in the breathing circuit during mechanical ventilation under the cooperation of the inflating device 4, and the gas pressure P of the differential pressure stabilization cavity 3 is enabled to be3And the pressure P of the gas in the breathing circuit during mechanical ventilationAirwayRemain in a non-equal equilibrium state, namely: p3＞PAirway，(P3-PAirway) The difference value is equal to a constant value (the exhaust pressure threshold value P of the one-way overflow exhaust valve 5)5) Namely: (P)3-PAirway)≈P5. While the pressure difference stabilizes the gas pressure P of the chamber 33And the gas pressure P of the sealing air bag 22Dynamic equilibrium, P2≈P3And then: (P)2-PAirway)≈P5。
In practical use, under the action of the inflator 4, when (P)3-PAirway)＞P5When (P)3-PAirway) Acting on the surface of the overflow valve 53 to open the overflow valve 53 to form a crack channel, and discharging the gas in the differential pressure stabilization cavity 3 through the crack channel, the overflow valve opening 54 and the exhaust port 52; at this time, the gas pressure in the differential pressure stabilization chamber 3 rapidly decreases when (P)3-PAirway)≈P5In the meantime, the excessive pressure valve 53 is closed again, the slit passage disappears, and the excessive pressure valve 53 and the excessive pressure valve opening 54 are restored to the sealed closed state again.
The inflating device 4 continuously inflates gas into the pressure difference stabilizing cavity 3 to provide a gas source for the sealed air bag 2. In fact, the pressure difference stabilizing chamber 3 only serves as a hinge for connecting the sealing air bag 2, the inflating device 4 and the one-way overflow exhaust valve 5, and the volume of the pressure difference stabilizing chamber is not excessively large. The air charging device 4 can be an air pump, and the process of a miniature air pump on the market is mature and is only 1-2cm3And the size can be completely used as a fitting.
The following problems are to be noted: when the pressure of the air passage is changed from the expiration phase with lower pressure to the expiration phase with higher pressure, the gas amount in the sealing air bag 2 also needs to be quickly supplemented, so that the air pressure in the sealing air bag 2 is quickly increased from a value slightly larger than the air passage pressure of the expiration phase to a value slightly larger than the air passage pressure of the inspiration phase, and the sealing performance of mechanical ventilation is influenced. That is, the inflator 4 must provide sufficient inflation rate to the pressure differential stabilization chamber 3 to meet the minimum gas volume requirement.
We address this issue as follows:
the volume of the sealed air bag 2 or the sealed air bag of the ventilation catheter is V2. The V is2Refers to the sum of the volumes of the sealing air bag 2 and the differential pressure stabilizing cavity 3, namely the connecting pipeline. Even the maximum model of the ventilator does not exceed 20ml (about 10ml in most cases), the limit value is taken as: v220 ml. The highest pressure of gas in the mechanical ventilation breathing circuit is PmaxMinimum pressure of Pmin. The gas pressure in the mechanical ventilation breathing circuit is the airway pressure of the patient in mechanical ventilation, the inhalation phase is high, normal people are generally under 15mmHg, special patients rarely exceed 30mmHg, and the highest adjustable value of a safety pressure valve of an anesthesia machine is taken here70 mmHg. The airway pressure of a patient subjected to mechanical ventilation is always positive, the expiratory phase airway pressure is generally not more than 5mmHg, and the limit value is 0 mmHg; the values here are relative values marked by taking the standard atmospheric pressure 760mmHg as a zero point, and the absolute pressure values are respectively: pmaxIs (760+70) mmHg 830 mmHg; pminThe value is (760+0) mmHg, 760 mmHg.
According to Boyle's law, it will be necessary to supplement into V2By conversion of gas to PminVolume of gas in time, volume VSupplement deviceComprises the following steps: vSupplement device≥(Pmax/Pmin-1)×V2；
In normal patients, the limit values are taken as follows: v2＝20ml、Pmax＝830mmHg、Pmin760mmHg, substitute for the above equation:
Vsupplement device≥[(830/760)-1]×20ml；
VSupplement device≥1.85ml；
The regional air pressure is related to the altitude, the higher the altitude is, the smaller the air pressure is, the earth and human inhabitation area is grown, the highest altitude is less than 4000 meters, and the air pressure is more than 460 mmHg; the limit values are respectively: v2＝20ml、Pmax＝(460+70)mmHg＝530mmHg、Pmin460mmHg, substituting the above formula VSupplement device≥(Pmax/Pmin-1)×V2：
VSupplement device≥[(530/460)-1]×20ml；
VSupplement device≥3.05ml；
When the patient needs to enter the hyperbaric oxygen chamber for treatment, the gas pressure of the hyperbaric oxygen chamber is 0.2-0.25MPa, namely 1520 and 1900 mmHg. Taking the limit values as follows: v2＝20ml、Pmax＝(1900+70)mmHg＝1970mmHg、Pmin1900mmHg, substituting the above formula
VSupplement device≥(Pmax/Pmin-1)×V2：
VSupplement device≥[(1970/1900)-1]×20ml；
VSupplement device≥0.74ml；
It is obvious that the inflator in the market is easyThe above requirements are met. What needs to be reminded is: because the invention maintains and maintains the air pressure of the sealed air bag 2 and the pressure P of the air in the breathing circuit during mechanical ventilationAirwayNon-isostatic dynamic equilibrium of (i.e., (P)2-PAirway)≈P5No special operation is needed no matter the high-pressure oxygen chamber is accessed. Only the various parts of the invention need to be kept working well.
As shown in figures 5-6, the connecting device for pressure difference stabilization of the invention comprises a pressure difference stabilization cavity 3, and an inflating device 4 and a one-way overflow exhaust valve 5 are arranged for communicating the pressure difference stabilization cavity 3. The air charging device 4 is provided with an air inlet 41 and an air outlet 42, the air outlet 42 is communicated with the pressure difference stabilizing cavity 3, and air can be charged into the pressure difference stabilizing cavity 3 through the air charging device 4. The overflow pressure exhaust valve 5 is provided with an air inlet 51 and an air outlet 52, the inner cavity of the overflow pressure exhaust valve 5 is provided with an overflow pressure valve 53 and an overflow pressure valve opening 54 which are matched, and the overflow pressure valve 53 is in stressed movable contact with the overflow pressure valve opening 54 at one side close to the air outlet 52. The air inlet 51 is communicated with the pressure difference stabilizing cavity 3, the pressure overflow valve 53 is contacted with the gas in the breathing circuit during mechanical ventilation at one side of the air outlet 52, and the pressure overflow gas in the pressure difference stabilizing cavity 3 can be discharged through the pressure overflow exhaust valve 5. The pressure difference stabilizing cavity 3 is communicated with an inflation fixing interface 6 matched with an inflation opening of the ventilation catheter and is provided with a respiration connecting pipe 7 matched with a respiration loop.
In the scheme, the body 1 of the ventilation catheter is replaced by the ventilation catheter, and the ventilation catheter is consistent with the existing ventilation catheter, and when the ventilation catheter is used, the inflation fixing interface 6 is only connected to an inflation port of the ventilation catheter, and the respiratory connecting pipe 7 is connected to a respiratory loop during mechanical ventilation. The working principle of the ventilation catheter comprises a single-cavity tracheal catheter, a double-cavity tracheal catheter, a bronchus stopper and a trachea incision ventilation pipe, and the like, is completely the same as the structure of the graph 1-4, is only arranged separately from the body 1 of the ventilation catheter, and is not described again here.
As shown in fig. 1, 3 and 5, the inlet 41 of the inflator 4 communicates with a mechanical ventilation breathing circuit, and the outlet 52 of the overflow vent valve 5 communicates with the mechanical ventilation breathing circuit. The air charging device 4 is pumped from the mechanical ventilation breathing loop and is charged into the differential pressure stable cavity 3, and the overflow pressure gas in the differential pressure stable cavity 3 is discharged into the mechanical ventilation breathing loop through the overflow pressure exhaust valve 5.
When the pressure relief valve works, the pressure and the gas flow state in all aspects are as follows (the cross section of the pressure relief valve 53 on the side close to the gas inlet 51 is S, and the air leakage threshold of the pressure relief exhaust valve 5 is P5):
firstly, after the trachea intubation is successful, the autonomous respiration of the patient stops, and the pressure in the airway of the patient is the external environment air pressure PEnvironment(s). The pressure relief valve 53 of the pressure relief exhaust valve 5 is stressed to F (P) at the side close to the exhaust port 52Environment(s)+P5) X S; the air charging device 4 of the invention starts to work, and draws air from the external environment, replenishes the air into the differential pressure stable cavity 3, and then enters the sealed air bag 2 or the ventilation catheter sealed bag, so that the air pressure in the sealed air bag 2 or the ventilation catheter sealed bag is quickly raised to (P)Environment(s)+P5) (ii) a After the instantaneous pressure is balanced, the inflating device 4 of the invention continuously pumps gas from the external environment and replenishes the gas into the sealed air bag 2 or the sealed air bag of the ventilation catheter, but the gas continuously replenished by the inflating device 4 makes the pressure of the gas in the differential pressure stable cavity 3 be greater than (P)Environment(s)+P5) The continuously supplemented air is ejected to the mechanical ventilation breathing circuit through the overflow valve opening 54 after the overflow valve 53 is pushed to one side of the exhaust port 52 in the overflow exhaust valve 5, and then enters the external environment.
② after connecting the respiratory loop, the respiratory equipment starts working, pumping gas into the patient's lungs, entering into the inspiratory phase, the patient's airway pressure PAirwayQuickly raised to the suction phase pressure PAir suction. Correspondingly, the pressure relief valve 53 of the pressure relief exhaust valve 5 is stressed by F (P) on the side close to the exhaust port 52Air suction+P5) And x S. At this time, the pressure of the pressure-relief valve 53 at the side of the air inlet 51 is (P)Environment(s)+P5) Pressure P less than one side of the exhaust port 52Air suction+P5) The overflow valve 53 in the overflow exhaust valve 5 closes the overflow valve opening 54; the air charging device 4 pumps air from the mechanical ventilation breathing circuit, replenishes the air into the differential pressure stable cavity 3 and then enters the sealed air bag 2 or the ventilation catheter sealed bag, so that the air pressure in the sealed air bag 2 or the ventilation catheter sealed bag is quickly changed from (P)Environment(s) of+P5) Is promoted to (P)Airway+P5) (ii) a After the instantaneous pressure is balanced, the inflating device 4 of the invention continuously pumps gas from the mechanical ventilation breathing loop to be supplemented into the sealed air bag 2 or the ventilation catheter sealed air bag, but the gas which is continuously supplemented by the inflating device 4 makes the pressure of the gas in the differential pressure stable cavity 3 be greater than (P)Airway+P5) The continuously supplemented air is ejected to the mechanical ventilation breathing circuit through the overflow valve opening 54 after the overflow valve 53 is pushed to one side of the exhaust port 52 in the overflow exhaust valve 5.
Thirdly, the breathing equipment stops pumping gas into the lungs of the patient after the inspiration phase is finished, the non-internal gas of the patient begins to be discharged under the elastic retraction force of the chest wall of the patient, and the airway pressure P of the patientAirwayQuickly drops to expiratory phase pressure PBreath. Correspondingly, the pressure relief valve 53 of the pressure relief exhaust valve 5 is stressed by F (P) on the side close to the exhaust port 52Breath+P5) And x S. At this time, the pressure of the pressure-relief valve 53 at the side of the air inlet 51 is (P)Air suction+P5) Pressure P greater than one side of the exhaust port 52Breath+P5) The overflow valve 53 in the overflow exhaust valve 5 is opened, and the gas in the sealed air bag 2 or the sealed air bag of the ventilation catheter and the gas in the differential pressure stable cavity 3 are exhausted to the mechanical ventilation breathing loop through the overflow valve opening 54; at the same time, the gas which is continuously supplemented into the pressure difference stabilization cavity 3 by the inflating device 4 is also discharged to the mechanical ventilation breathing circuit through the pressure overflow valve opening 54 until the gas pressure in the sealed air bag 2 or the ventilation catheter sealed air bag is reduced to (P)Breath+P5). Subsequent exhalation phase, maintenance of gas pressure (P) in the sealed balloon 2 or the sealed balloon of the airway tubeBreath+P5) The gas in the sealed air sac 2 or the air duct sealed air sac is not discharged into the pressure difference stable cavity 3, but the inflating device 4 continues to supplement the gas into the pressure difference stable cavity 3, and only the supplemented gas is continuously discharged into the mechanical ventilation breathing circuit through the overflow valve opening 54. At this time, in the relief vent valve 5, the relief valve 53 is maintained in a high-frequency open-close alternating state at the relief orifice 54.
Fourthly, after the expiration phase, the breathing equipment pumps gas into the lungs of the patient again, the gas enters an inspiration phase, and the airway pressure P of the patientAirwayQuickly raised to the suction phase pressure PAir suction. Correspondingly, the pressure relief valve 53 of the pressure relief exhaust valve 5 is stressed by F (P) on the side close to the exhaust port 52Air suction+P5) And x S. At this time, the pressure of the pressure-relief valve 53 at the side of the air inlet 51 is (P)Breath+P5) Pressure P less than one side of the exhaust port 52Air suction+P5) The overflow valve 53 in the overflow exhaust valve 5 closes the overflow valve opening 54; the inflating device 4 extracts gas from the mechanical ventilation breathing circuit to supplement the gas into the differential pressure stable cavity 3 and then enters the sealed air bag 2 or the ventilation catheter sealed bag, so that the gas pressure in the sealed air bag 2 or the ventilation catheter sealed bag is quickly increased by (P)Breath+ P5) to (P)Air suction+P5) (ii) a After the instantaneous pressure is balanced, the inflating device 4 of the invention continuously pumps gas from the mechanical ventilation breathing loop to be supplemented into the sealed air bag 2 or the ventilation catheter sealed air bag, but the gas which is continuously supplemented by the inflating device 4 makes the pressure of the gas in the differential pressure stable cavity 3 be greater than (P)Air suction+P5) The continuously supplemented air is ejected to the mechanical ventilation breathing circuit through the overflow valve opening 54 after the overflow valve 53 is pushed to one side of the exhaust port 52 in the overflow exhaust valve 5.
And fifthly, repeatedly circulating in the expiratory phase and the inspiratory phase until the mechanical ventilation is finished, recovering the spontaneous respiration of the patient, and detaching the respiratory circuit from the respiratory equipment. When the patient breathes autonomously, the inside of the air passage is negative pressure PAutonomous system(less than the ambient pressure) is less than P during mechanical ventilationBreathAnd PAir suction. At this time, correspondingly, the pressure relief valve 53 of the pressure relief exhaust valve 5 is forced to F ═ P (P) on the side near the exhaust port 52Air suction+P5) X S, or is (P)Air suction+P5) And x S. At this time, the pressure of the pressure-relief valve 53 at the side of the air inlet 51 is (P)Breath+P5) Or (P)Air suction+P5) Greater than the pressure at the side of the exhaust port 52). The overflow valve 53 in the overflow exhaust valve 5 is opened, the overflow valve 53 in the overflow exhaust valve 5 is pushed open, and the gas in the sealed air bag 2 or the sealed air bag of the ventilation catheter and the gas in the differential pressure stable cavity 3 are exhausted to the external environment through the overflow valve opening 54; meanwhile, the gas which is continuously supplemented into the pressure difference stabilizing cavity 3 by the inflating device 4 is exhausted to the mechanical ventilation breathing loop through the pressure overflow valve opening 54 until the sealing air bag 2 or the ventilation catheter is sealedThe gas pressure in the capsule drops to PAutonomous system. After the spontaneous respiration of the patient is completely recovered after observation for a period of time, the inflation device 4 can be closed, the gas in the sealed air bag 2 is pumped out, and the ventilation catheter body 1 or the ventilation catheter is pulled out.
As shown in fig. 2, 4 and 6, the inlet 41 of the inflator 4 communicates with the outside, and the outlet 52 of the overflow vent valve 5 communicates with the outside. The pressure overflow valve 53 of the pressure overflow exhaust valve 5 is hermetically communicated with the mechanical ventilation breathing loop and is provided with a pressure induction soft membrane bag 55, and the exhaust port 52 is arranged outside the cavity of the soft membrane bag 55. One side of the inner part of the soft membrane bag 55 is hermetically connected with the overflow pressure valve 53, and the overflow pressure valve 53 is supported on the overflow pressure valve opening 54. One side of the inside of the pressure overflow valve 53 is communicated with the breathing circuit through the soft membrane bag 55, and the gas pressure of the breathing circuit can act on the pressure overflow valve 53 through one side of the inside of the soft membrane bag 55. And the gas in the sealing air sac 2 or the air duct acts on the overflow pressure valve 53 on the outer side of the soft membrane bag 55. And the vent 52 of the overflow vent valve 5 is disposed outside the soft membrane bag 55 at a side of the overflow flap opening 54 adjacent to the soft membrane bag 55. The working principle of the air inflation device is basically consistent with that of the air inflation device, and the air inflation device 4 pumps air from the external environment to be supplemented into the differential pressure stabilizing cavity 3 and the sealed air bag 2 or the sealed air bag of the ventilation catheter in any state. As shown in fig. 8, when the gas overflowing from the sealed airbag 2 is exhausted through the overflow exhaust valve 5, the gas is blocked by the soft film bag 55, and after the overflow valve 53 is pushed open, the gas cannot enter the breathing circuit, but is exhausted to the external environment through the exhaust port 52 adjacent to the outside of the soft film bag 55. The advantage is that no matter the air is supplemented to the sealed air bag 2 or the air duct sealed bag or exhausted, the air duct body 1 or the air duct and the inner cavity of the breathing circuit are isolated, and the ventilation quantity in the mechanical ventilation process cannot be influenced. The solution according to claim 3 is realized in fig. 1, 3, 5, where the overpressure gas overflow circuit is shown in fig. 7, and the amount of gas difference is very small, almost negligibly small compared to the volume of several hundred milliliters during mechanical ventilation, due to the fact that either the make-up gas or the exhaust gas comes from the breathing circuit.
Further, the overflow vent valve 5 comprises an electromagnetic vent valve or a spring vent valve, and the overflow vent valve 5 can be adjusted by adjusting the deformation amplitude of the resistor or the springAn exhaust threshold. The miniaturization of the electromagnetic exhaust valve on the market is only 1-2cm2The size, the price are extremely low, the quality is stable, and the scale production can be completely realized. If an electromagnetic exhaust valve is adopted, power supply needs to be distributed, the inflating device can also adopt a miniature electric inflating pump, and the miniature electric inflating pump is very common in the market, also needs to be distributed with power supply, and can adopt a common power supply. If the power of the electric inflator pump or the exhaust threshold of the electromagnetic exhaust valve needs to be adjusted, only the adjustable resistor needs to be claimed, and details are not repeated here. The spring exhaust valves are adopted in fig. 1-6 of the invention, the structures are quite common, if the exhaust threshold of the spring exhaust valve needs to be adjusted, the degree of compression deformation of the spring can be adjusted, and the spring exhaust valves are also common structures, and are not described again here.
Furthermore, the mechanical ventilation breathing circuit comprises a ventilation catheter tube body 1 and a breathing connecting tube 7, wherein two ends of the breathing connecting tube are respectively matched with the ventilation catheter tube body 1 and a breathing threaded tube. Mechanical ventilation breathing circuits are a common name in anesthesia and include various conduits that communicate with the respiratory tract of a patient, such as: the ventilation catheter body 1, the respirator threaded pipe and the respiratory connecting pipe 7. The breath connection tube 7 is also a structure commonly used in anesthesia, and has two ends with fixed apertures, which can be connected with the front and rear breathing tubes, respectively, and will not be described herein.
Further, the exhaust threshold value P of the overflow exhaust valve 55For the pressure P of the gas in the pressure difference stabilizing chamber 33With the pressure P of the gas in the mechanical ventilation breathing circuitAirwayThe difference between them. When (P)3-PAirway)＞P5When the pressure-overflow valve 53 leaves the pressure-overflow valve opening 54, the gas in the pressure-difference stabilization cavity 3 is exhausted through the pressure-overflow exhaust valve 5; when (P)3-PAirway)＜P5When the pressure relief valve 53 is used, the pressure relief valve opening 54 is blocked, and the gas in the pressure difference stabilization cavity 3 cannot be discharged through the pressure relief exhaust valve 5. This is described in detail in the foregoing, and will not be described in detail here.
Further, the exhaust threshold value P of the overflow exhaust valve 55Less than 15 mmHg. In the scheme, the pressure of the sealing air bag 2 to the inner wall of the air passage is (P)Airway+P5) The pressure of the expiratory phase airway is more than 3mmHg and the air bag 2 is sealedThe pressure on the inner wall of the airway is < 18mmHg (15mmHg +3 mmHg). The pressure of the air bag on the inner wall of the airway is greatly reduced by being set to be 30mmHg in the current market, and the practical clinical significance is achieved. In practice, P5The most suitable pressure is 5mmHg, the corresponding expiratory phase airway pressure is less than 8mmHg, and in the pressure range, the blood supply of the inner wall of the airway has no influence, so that the pressure damage of the air bag to the inner wall of the airway can be avoided.
Further, a gas pressure sensor is arranged in the sealed air bag 2 or the sealed air bag of the ventilation catheter communicated with the body 1 of the ventilation catheter, and the gas pressure P in the sealed air bag 2 or the sealed air bag of the ventilation catheter communicated with the body 1 of the ventilation catheter is monitored and displayed2(ii) a A gas pressure sensor is arranged in the mechanical ventilation and respiration loop and is communicated with the mechanical ventilation and respiration loop to monitor and display the gas pressure P in the mechanical ventilation and respiration loopAirway. Respectively provided with a gas pressure sensor for monitoring P2And PAirwayThe significance lies in that: firstly, the pressure state of the airway of a patient during mechanical ventilation can be observed in time; the pressing state of the air bag on the inner wall of the air passage can be observed in time during mechanical ventilation; thirdly, dynamic monitoring P2And PAirwayDifference (P) of2-PAirway) Difference (P)2-PAirway) The air duct sealing performance can be ensured when the air duct is mechanically ventilated; otherwise, it is necessary to turn up the power of the inflator 4. As shown in FIGS. 9 and 10, the pressure of P2 and the P airway in the two most common respiratory modes is plotted along the time axis, and if P is monitored dynamically at the same time2And PAirwayThe pressure value is adjusted only by adjusting the power of the air charging device 4 to be proper so as to lead P to be2And PAirwayThe pressure time axis lines are respectively separated and never intersected, no intersection point exists, the mechanical ventilation can be ensured to be airtight, and simultaneously P2And PAirwayPressure difference of P5The actual requirements of clinical application can be met by left and right fluctuation.
Further, as shown in fig. 1-4, the differential pressure stabilization chamber 3 is communicated with the sealed airbag 2 through an inflation tube 8, the inflation tube 8 is provided with a switch 81, and the inflation tube 8 is provided with a pressure valve inflation port 82 at a side of the switch 81 adjacent to the sealed airbag 2. Through be equipped with switch 81 at gas tube 8 to set up pressure valve inflation inlet 82, can realize: firstly, before the trachea cannula operation, the air in the sealed air bag 2 is exhausted through the inflation inlet 82 of the pressure valve, so that the phenomenon that the air bag is over expanded and the cannula is difficult to insert is avoided during the cannula operation, and the cannula damage is reduced; if the inflation device 4 or the overflow exhaust valve 5 has a fault, the switch 81 is closed, and a proper amount of gas is filled into the sealed air bag 2 through the inflation port 82 of the pressure valve, so that the function of the traditional tracheal catheter can be achieved; and thirdly, when the mechanical ventilation is finished and the tracheal catheter needs to be pulled out, the switch 81 is closed, and the gas in the sealed air bag 2 is exhausted through the inflation inlet 82 of the pressure valve, so that the air bag is prevented from being excessively expanded, and the damage of tube pulling is reduced.
In a word, through the arrangement of the pressure difference stabilizing cavity, the pressure of the gas in the sealed air bag is automatically adjusted by the gas in the breathing circuit through the pressure difference stabilizing cavity during mechanical ventilation, so that the pressure of the gas in the sealed air bag is greater than the pressure of the gas in the breathing circuit, and the pressure difference value is stabilized at a proper value; the pressure of the ventilation catheter sealing air bag is synchronously and dynamically changed along with the airway pressure of mechanical ventilation, and in an expiratory phase with lower mechanical ventilation airway pressure, the air pressure in the sealing air bag is lower, the blood circulation of tracheal mucosa is recovered, and the tracheal mucosa is prevented from being damaged.
Claims (10)
1. The utility model provides a stable air duct of pressure differential, includes air duct body (1), and air duct body (1) head segment is equipped with sealed gasbag (2), its characterized in that: the sealed air bag (2) is communicated with a pressure difference stabilizing cavity (3); the pressure difference stabilizing cavity (3) is communicated with an air charging device (4) and a one-way pressure overflow exhaust valve (5); the air charging device (4) is provided with an air inlet (41) and an air outlet (42); the air outlet (42) is communicated with the differential pressure stable cavity (3), and air can be filled into the differential pressure stable cavity (3) through the air charging device (4); the overflow pressure exhaust valve (5) is provided with an air inlet (51) and an air outlet (52), the inner cavity of the overflow pressure exhaust valve (5) is provided with an overflow pressure valve (53) and an overflow pressure valve opening (54) which are matched, and the overflow pressure valve (53) is in stressed movable contact with the overflow pressure valve opening (54) at one side close to the air outlet (52); the air inlet (51) is communicated with the differential pressure stabilizing cavity (3), the pressure overflow valve (53) is in contact with the gas in the breathing loop during mechanical ventilation at one side of the air outlet (52), and the pressure overflow gas in the differential pressure stabilizing cavity (3) can be discharged through the pressure overflow exhaust valve (5).
2. A pressure differential stabilizing connection, comprising: comprises a differential pressure stabilizing cavity (3), an air charging device (4) and a one-way pressure overflow exhaust valve (5) are arranged and communicated with the differential pressure stabilizing cavity (3); the air charging device (4) is provided with an air inlet (41) and an air outlet (42); the air outlet (42) is communicated with the differential pressure stable cavity (3), and air can be filled into the differential pressure stable cavity (3) through the air charging device (4); the overflow pressure exhaust valve (5) is provided with an air inlet (51) and an air outlet (52), the inner cavity of the overflow pressure exhaust valve (5) is provided with an overflow pressure valve (53) and an overflow pressure valve opening (54) which are matched, and the overflow pressure valve (53) is in stressed movable contact with the overflow pressure valve opening (54) at one side close to the air outlet (52); the air inlet (51) is communicated with the differential pressure stabilizing cavity (3), the pressure overflowing valve (53) is in contact with air in the breathing loop during mechanical ventilation at one side of the air outlet (52), and the pressure overflowing air in the differential pressure stabilizing cavity (3) can be discharged through the pressure overflowing exhaust valve (5); the pressure difference stabilizing cavity (3) is communicated with an inflation fixing interface (6) matched with an inflation port of the ventilation catheter and is provided with a respiration connecting pipe (7) matched with a respiration loop.
3. The pressure differential-stabilized airway tube and connector apparatus of claims 1 or 2, wherein: the air inlet (41) of the air charging device (4) is communicated with a mechanical ventilation breathing circuit; an exhaust port (52) of the overflow exhaust valve (5) is communicated with the mechanical ventilation breathing loop; the air charging device (4) is pumped from the mechanical ventilation breathing loop and is charged into the differential pressure stable cavity (3), and the overflow gas in the differential pressure stable cavity (3) is discharged into the mechanical ventilation breathing loop through the overflow exhaust valve (5).
4. The pressure differential-stabilized airway tube and connector apparatus of claims 1 or 2, wherein: the air inlet (41) of the inflation device (4) is communicated with the outside, and the air outlet (52) of the overflow exhaust valve (5) is communicated with the outside; the pressure overflow valve (53) of the pressure overflow exhaust valve (5) is communicated with the mechanical ventilation breathing loop in a sealing way to be provided with a pressure induction soft membrane bag (55), and the exhaust port (52) is arranged outside the cavity of the soft membrane bag (55).
5. The pressure differential stabilizing airway tube and connector apparatus according to claim 1 or claim 2 wherein: the overflow exhaust valve (5) comprises an electromagnetic exhaust valve or a spring exhaust valve, and the exhaust threshold value of the overflow exhaust valve (5) can be adjusted by adjusting the deformation amplitude of a resistor or a spring.
6. The pressure differential-stabilized airway tube of claim 1, wherein: the mechanical ventilation breathing loop comprises a ventilation catheter tube body (1) and a breathing connecting tube (7) of which two ends are respectively matched with the ventilation catheter tube body (1) and a breathing threaded tube.
7. The pressure differential-stabilized airway tube and connection device of claims 1, 2 or 4, wherein: an exhaust threshold value P of the pressure relief exhaust valve (5)5For the pressure P of the gas in the pressure difference stabilizing cavity (3)3With the pressure P of the gas in the mechanical ventilation breathing circuitAirwayThe difference between them; when (P)3-PAirway)＞P5When the pressure relief valve (53) leaves the pressure relief valve opening (54), the gas in the pressure difference stabilizing cavity (3) is exhausted through the pressure relief exhaust valve (5); when (P)3-PAirway)＜P5When the pressure relief valve (53) is used, the pressure relief valve opening (54) is blocked, and the gas in the pressure difference stabilizing cavity (3) can not be discharged through the pressure relief exhaust valve (5).
8. The pressure differential stabilizing airway tube and connector apparatus of claim 7 wherein: an exhaust threshold value P of the pressure relief exhaust valve (5)5＜15mmHg。
9. The pressure differential-stabilized airway tube and connector apparatus of claims 1 or 2, wherein: the sealed air bag (2) or the sealed air bag of the ventilation catheter communicated with the catheter body (1) is provided with an air pressure sensor which monitors and displays the air pressure P in the sealed air bag (2) or the sealed air bag of the ventilation catheter body (1)2(ii) a A gas pressure sensor is arranged in the mechanical ventilation and respiration loop and is communicated with the mechanical ventilation and respiration loop to monitor and display the gas pressure P in the mechanical ventilation and respiration loopAirway。
10. The pressure differential stabilizing airway tube and connector apparatus of claim 1 wherein: the pressure difference stabilizing cavity (3) is communicated with the sealed air bag (2) through an inflation tube (8), the inflation tube (8) is provided with a switch (81), and the inflation tube (8) is provided with a pressure valve inflation inlet (82) at one side of the switch (81) close to the sealed air bag (2).
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| Application Number | Priority Date | Filing Date | Title |
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| CN202210117334.1A CN114432559A (en) | 2022-02-08 | 2022-02-08 | Air duct with stable pressure difference and connecting device |
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| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202210117334.1A CN114432559A (en) | 2022-02-08 | 2022-02-08 | Air duct with stable pressure difference and connecting device |
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| CN114432559A true CN114432559A (en) | 2022-05-06 |
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| CN202210117334.1A Pending CN114432559A (en) | 2022-02-08 | 2022-02-08 | Air duct with stable pressure difference and connecting device |
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Cited By (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN115252994A (en) * | 2022-08-10 | 2022-11-01 | 江培颜 | Method and device for automatically adjusting tracheal catheter cuff pressure synchronously with breathing machine |
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| CN203802913U (en) * | 2014-04-15 | 2014-09-03 | 四川大学华西医院 | Artificial airway |
| CN204411457U (en) * | 2014-12-03 | 2015-06-24 | 杭州市红十字会医院 | With the endotracheal tube of synchronous airway pressure formula balloonet |
| CN110237390A (en) * | 2019-07-17 | 2019-09-17 | 浦其斌 | Artificial airway |
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| US5265593A (en) * | 1991-05-02 | 1993-11-30 | Odland Rick M | Balloon-tipped catheter ventilation system and method for using same having rhythmically inflated and deflated balloon |
| CN102120056A (en) * | 2010-01-10 | 2011-07-13 | 江伟 | Bronchial catheter with single cavity and double sacs |
| CN203802913U (en) * | 2014-04-15 | 2014-09-03 | 四川大学华西医院 | Artificial airway |
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