JPH11267215A - Respirator - Google Patents

Abstract

PROBLEM TO BE SOLVED: To open a secretion closing bronchial tubes by an air hammer effect, to make oxygen reach all over lungs, to fluidize the secretion covering alveoli, to urge expectoration, to improve the efficiency of the exchange of the oxygen and carbon dioxide gas by the diffusion effect of impulsive inspiration and to improve treatment effects by supplying impulsiveness to inspiration introduced into the lungs of a patient. SOLUTION: This respirator driven by pressurized gas uses a special shock wave generator 16 for generating shock waves by the action of a sliding venturi 39. Gas is introduced to a device at the pressure of 1.0-6.0 kg/cm<2> and the gas flow is led to an oscillator, converted to intermittent gas there, then led to the shock wave generator 16 and converted to impulsive respiration gas.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a ventilator for assisting respiration of a patient with a respiratory disease, wherein air, oxygen or a mixed gas of air and oxygen having an impact is inhaled into a patient's lung. Injects frequently, fluidizes secretions that block the bronchi, opens gas passages, promotes sputum, and sprays water or drugs that have been nebulized with a nebulizer (erosol generator). The present invention relates to a new respiratory assist device that is capable of spreading to the corners of the lungs on an inspiratory inhalation to enhance the therapeutic effect.

[0002]

2. Description of the Related Art The number of patients with chronic respiratory diseases is considerable in Japan, and tends to increase with aging. Not only patients with such chronic respiratory diseases, for example,
Clinicians often experience inadequate lung sputum after surgery that can lead to complications, often with severe consequences, and sometimes even death. That is.

[0003] Furthermore, in the case of patients with chronic obstructive pulmonary disease (COPD), the lungs are actually covered with secretions, which are also the source of sputum, and no matter how high the concentration of oxygen, breathing assistance is provided. The exchange of oxygen and carbon dioxide does not work well due to the sequestering action of the secretory film and cannot improve the patient's symptoms.

[0004] Moreover, it is the current medical situation that there is almost no effective method of this improvement. It is also known that secretions present in the lungs have various bad effects. For example, it is a frequent phenomenon that the bronchi or peripheral small bronchi that introduces air into various parts of the lungs are covered with the presence of sticky secretions, and the gas passage is completely obstructed. A patient with weak physical strength cannot sputum on his own, causing so-called dyspnea.

[0005] In conventional treatment methods, a high concentration of oxygen is introduced into the lungs of a patient to take measures to activate the breathing at all, or a high-concentration oxygen is precisely controlled by a device. Attempts have been made to introduce it into the lungs frequently, with some success, but none of the respiratory aids offers a treatment that actively removes secretions that cover the bronchi and alveoli. there were.

[0006] Until now, a jet stream utilizing the Venturi effect has been used, and treatment with this jet-type inspired gas has been attempted. However, the jet stream generated by the Venturi tube has a weak force and the secretion in the lungs is weakened. It is far from clearing fluids and secretions that occlude the bronchus. There were also problems, and the emergence of a revolutionary new ventilator was awaited.

The inventor of the present invention has developed a completely new idea to achieve an effective assisting effect which cannot be achieved by the conventional inspiratory force, in order to introduce the inspiratory breath through the bronchi into the patient's lungs. The present inventors have arrived at the present invention as a result of repeated studies and earnest studies toward realization thereof. The present invention makes use of the air hammer effect, ie, "percussion", by the shock introduction of inspiratory inspiration in the lungs, in other words, the present invention refers to an intrapulmonary percussion (impact) ventilation therapy (IPV). It paves the way for the introduction of new treatments for lung disease.

[0008] The basic idea and its effect is to give a favorable impact to the inspired air introduced into the lungs. By introducing the inhalation with a shock wave, obstructive secretions that obstruct the passage of gas in the bronchi or peripheral bronchi are fluidized and removed by the percussion effect, securing the gas flow path that was covered with secretions until then, It is possible to contribute to the effective exchange of oxygen-carbon dioxide gas.

That is, the first effect of the present invention resides in the opening of the blocked portion of the bronchus by percussion.

[0010] In addition, when the gas exchange site of the alveoli is covered with a sticky secretion (the excreted matter is sputum) and the gas exchange of oxygen-carbon dioxide gas is substantially hindered,
It fluidizes the air by the air hammer effect of the shock wave, enables sputum as sputum, and effectively removes the film of secretions, thereby removing the elements that have hindered gas exchange and achieving effective respiratory assistance. You can do it.

That is, the second effect of the present invention resides in fluidization of secretions in the lung.

A third effect provided by the present invention is a gas stirring, mixing and diffusion effect by percussion after gas exchange in the lungs. In other words, the place where the gas was exchanged is covered with carbon dioxide gas that has been absorbed and released by oxygen, and if this carbon dioxide gas is not efficiently removed and replaced with oxygen, effective oxygen The lack of supply is self-evident.

[0013] That is, percussion remarkably promotes the diffusion effect by mixing and stirring the gas, and the oxygen-carbon dioxide gas replacement effect.

Further, as a fourth effect, the nebulizer enables the nebulized medicine to reach every corner of the lungs by percussion, thereby enhancing the medicinal effect and improving the curability.

That is, the effects of the present invention are as follows: (1) an effect of securing a flow passage for removing obstruction of the bronchi by percussion; (2) a fluidization and sputum promoting effect by percussion of secretions in the lung; and (3) a gas by percussion. Diffusion effect by effective mixing and agitation of gas after exchange and improvement of gas exchange efficiency associated therewith, and (4) effective diffusion effect of drug by percussion are summarized in four points.

The present invention provides means for realizing the above four effects.

Looking at the current state of treatment for pulmonary diseases, patients with respiratory disorders breathe high-oxygen-concentrated gas through the nose, etc., and in the case of severe patients, support measures such as supporting breathing with 100% oxygen. Has been taken. However, no matter how high oxygen concentration is introduced into the lungs of a patient, nothing can be achieved if the bronchi, which is a conduit for oxygen to the human body, is obstructed, and replacement of oxygen and carbon dioxide gas cannot be achieved. Naturally, treatment efficiency will not increase if the field is covered with secretions and interferes with gas exchange.

The present inventor has focused on the following points in order to solve such a problem. That is, (1) the perspiration is introduced into the lungs. (2) Percussion is performed at a high frequency, and percussion air is introduced a plurality of times (for example, several to thirty times) within one intake period.
(3) The frequency of percussion is set to about 10 to 600 times / minute to make it effective. (4) Provide a break during the percussion period to allow sputum for secretions that have fallen off due to fluidization. (5) The wedge pressure (wedge pressure) in the lung, that is, the lung airway pressure is ideally 15
４５45 cm · H ₂ O.

Further, the inventor of the present invention (6) reduces the weight (easy to carry), (7) reduces the size (can be carried anywhere), and (8) uses electricity From the standpoint of practical use and additional treatment diversity, such as driving only by gas pressure (can be used anywhere), (9) simplifying operation, and (10) making it as safe as possible. The present invention has been completed as a result of a study deemed necessary and continued for its realization.

As described above, the ventilator of the present invention can be used anywhere as long as there is a pressurized gas source (such as a supply pipe from a gas tank or a gas cylinder). A built-in compressor or a combined use of an external compressor to prepare a pressurized gas of air from the atmosphere so that it can be used at home or while traveling, and drive this ventilator to use for treatment You can also.

According to the present invention, a shock wave generating device provided with a special function for injecting a shocking intake air (Japanese Patent Application Laid-open No.
2) Utilization of Japanese Patent Application Laid-Open No. 2-16149), in other words, the present invention makes full use of the function of the shock wave generator to inject inhalation into the lungs of a patient with an air hammer effect by percussion. The present invention provides a new ventilator system for creating an unprecedented method for intrapulmonary shock ventilation, which was completed in cooperation with the advice of Dr. Forrest Bird, the inventor of the shock wave generator.

In other words, the present invention makes full use of the function of the shock wave generator and applies it to a ventilator,
A practical ventilator system that solves many problems up to now and has a great effect, and does not use any electric control mechanism, but uses a pressurized gas to drive a drooling artificial respirator. This is a completed respiratory organ.

The difference between the effect of the present shock wave generator and the effect of the jet flow by the conventional Venturi tube will be briefly described, and the difference will be described.

The conventional jet flow system applies the principle that when a gas is injected from a high-pressure gas source through a thin tube as shown in FIG. 8, the high-speed jet flow draws in surrounding gas by the Venturi effect. A large amount of gas can be sent into a patient's airway within a short inhalation time. Switching between inspiration and expiration can be performed by a conventionally known rotary ball bearing, a fluid element system,
This is performed by injecting or stopping a jet stream by an electromagnetic valve or the like.

In this case, the jet stream is intermittently supplied to the patient's airway, but a considerable pressure is maintained even when switching to exhalation.

On the other hand, the shock wave generator used in the present invention is:
It incorporates a sliding venturi, the structure of which is shown in FIG. More specifically, the shock wave generator 16 used in the present invention is a cylindrical body having a sliding venturi 39 built therein. The sliding venturi is formed by an intermittent positive pressure gas obtained by using an oscillator 6 driven by a pressurized gas. 39 repeatedly moves back and forth, whereby the tip of the sliding venturi 39 opens and closes to the atmosphere, and when the intermittent gas flows in, it is instantaneously blocked, and a large amount of positive pressure gas is jetted by the venturi effect. Further, when the intermittent gas is stopped, the gas is instantaneously opened to release the gas in the shock wave generator 16 to the atmosphere, and the pressure load disappears.
This functional venturi effect converts the intermittent jet flow accelerated and supplied into an intermittent shock wave and supplies it to the patient's airway, and when the shock wave stops, instantaneously reduces the patient's airway pressure to atmospheric pressure. To facilitate breathing.

The details will be described below with reference to FIG.

FIG. 4 shows a cross section of the shock wave generator 16 used in the present invention. During inhalation, the diaphragm 47 in the shock wave generator 16 expands to the right to move the sliding venturi 39 to the right, and the mouthpiece 17
A route leading to the patient's airway is formed in a closed tubular body (see FIG. 4B), and the jet stream is effectively supplied to the patient. On the other hand, when the supply of the gas to the left intermittent gas supply port 37 is interrupted, that is, stopped, the sliding venturi 39 instantaneously returns to the left by the action of the spring 45 to form a gap in the closed tubular body ( (See FIG. 4A.) The gas is released to the atmosphere, and the pressure instantaneously becomes the atmospheric pressure. Due to this repetition, the jet flow rises and disappears drastically. For this reason, the respirator of the present invention to which the shock wave generator 16 is applied can provide a suitable shock (percussion) to the inhalation supplied to the patient, and the high frequency of the conventional jet flow can be achieved. Is essentially different from the ventilator. This is a revolutionary ventilator that provides the medical community with a new treatment, which can be called intrapulmonary shock ventilation. In addition, the problem of the gradual increase in the patient's lung pressure, which was a problem of the conventional high-frequency jet ventilator, can be solved.

[0029]

The features of the present invention are enumerated below as follows.

One of the features of the present invention is that the respirator is driven very precisely by pressurized gas without using electricity for driving.

A further feature of the present invention is that it allows the patient to be provided with inspiratory inspiratory gas and provides a new therapy, also referred to as intrapulmonary impact ventilation.

One of the features of the present invention is that it is small, light, and portable. To this end, a housing corresponding to the drive unit of the respirator and an assembly ( Accessories that summarize accessories)
And that the entire structure can be separated and decomposed as desired. Another object of the present invention is to facilitate the operation of controlling each function by holding it with one hand when a portable device is used.

One of the features of the present invention is that the housing, the connecting assembly, and each part of the assembly can be easily removed, disassembled, and assembled by means such as simple insertion and fitting.

Further, one of the features of the present invention is that when the portable device is made portable, the assembly of the nebulizer and the shock wave generator constituting the connecting assembly is regulated and set to a size that can be held by one hand of a person. It is downsized so that the operation of controlling the functions can be easily performed with a fingertip.

As will be described in detail later, for example, the patient holds the nebulizer part with one hand and operates the ventilator.
With a simple operation of pressing the push button with the thumb of the hand holding the nebulizer, the treatment of the intrapulmonary shock ventilation proposed in the present invention can be easily performed. For this purpose, the container of the nebulizer of the present invention has a maximum diameter (outer diameter in the case of a cylindrical shape) of 80 mm or less, 20 mm or more, preferably 60 mm or less, 30 mm or more, more preferably 5 mm or less.
It is preferably 0 mm or less and 40 mm or more. The most preferred diameter is around 45 mm. If the diameter is larger than 80 mm, it is difficult to hold the same with one hand, and if it is less than 20 mm, it is difficult to hold the hand, and it is difficult to press a button. In addition, the shortest distance between the center of the push button for the respiratory operation to activate the intrapulmonary shock ventilation and the lid above the nebulizer is 40.
mm or less, more preferably 30 mm or less, and even more preferably 25 mm or less.

This is because if the distance between the lid of the nebulizer and the button exceeds a certain distance, it becomes impossible to hold the nebulizer and operate the push button with one hand.

The lower limit of the size of the nebulizer container is also limited, since the nebulizer container preferably has a capacity suitable for charging a drug necessary for one treatment.

One of the features of the present invention is that disinfection of the connecting assembly is extremely easy and reliable.
That is, since the housing, the connecting assembly, and each part of the assembly can be easily disassembled into a convenient size, handling of each part when disinfecting is not complicated, and it is possible to easily disinfect the details.

One of the features of the present invention is that only a single pressurized gas source is used. In order to function as a ventilator precisely, an orifice is cleverly arranged in a circuit in the housing to balance the gas flow. The point is that it has achieved its purpose.

One of the features of the present invention is that the safety of the patient is taken into consideration, and a switch is provided so that the ventilator is activated only while the patient or the medical staff is pushing the push button switch. On the point.

The present invention will be described in detail. This is a ventilator for performing intrapulmonary shock ventilation therapy by using a shock wave generated by the operation of a shock wave generator as an inspired gas and driven by a pressurized gas. A part of the intake gas is guided to a nebulizer to become a humidified spray gas, and another part of the introduced intake gas is converted into an intermittent flow, and then guided to the shock wave generator to be given an impact, The present invention provides a system for merging with water or a nebulizing gas containing a drug from the nebulizer to administer to a patient.

More specifically, the present invention relates to a ventilator which is driven by a pressurized gas and performs shock ventilation ventilation treatment in a lung by using a shock wave generated by the operation of a shock wave generator as inspiration.
The ventilator is composed of a connection assembly including a housing and a shock wave generator, and the housing is provided with a gas inlet for introducing a gas, and a part of the gas introduced into the gas inlet is a continuous flow. Another continuous flow branched from the gas introduced into the casing as a guide to the nebulizer is converted into an intermittent flow by an oscillator cartridge and guided to the shock wave generator outside the casing, and the atomizing gas stream from the nebulizer is A ventilator characterized by being merged with a shock wave generator and converted into intermittent shock gas.

Further, the present invention relates to a ventilator for performing in-pulmonary shock ventilation therapy, wherein the respirator is driven by a pressurized gas and uses the shock wave generated by the operation of the shock wave generator as inhalation. Consisting of a connection assembly including a generator, the housing is provided with a gas inlet for introducing gas, and a part of the gas introduced into the gas inlet is guided to the nebulizer as a continuous flow, and the housing is Another continuous flow branched from the gas introduced into the chamber is converted into an intermittent flow by the oscillator cartridge and guided to the shock wave generator outside the housing, and the spray gas stream from the nebulizer merges with the shock wave generator to generate a shock wave. A ventilator that is converted into intermittent shock breathing gas by a device, wherein a remote switch is disposed on a tubular body connecting the nebulizer and the shock wave generator, By the action of the switch is a ventilator intermittent air flow from the oscillator cartridge, characterized in that the flow in the shock wave generating apparatus.

Further, the present invention relates to a ventilator for performing shock ventilation treatment in the lungs by using a shock wave generated by the operation of a shock wave generating device and driven by a pressurized gas, the whole being contained in a housing. The housing comprises a gas inlet for introducing gas, and at least two sockets that can be attached to and detached from the tube. An oscillator cartridge that converts the flow into an intermittent flow, a nebulizer and a shock wave generator as a connecting assembly are arranged outside the housing, and the first socket connects the continuous flow leading to the gas inlet in the housing to the nebulizer outside the housing. Connect with a tube,
The second socket is a ventilator characterized in that a gas flow converted into an intermittent flow by an oscillator cartridge inside the housing is connected to a shock wave generator outside the housing by a tube.

Another feature of the present invention is to provide a respiratory apparatus that embodies deep consideration for prevention of infection by a device used by a patient. Generally speaking, patients who need a ventilator often carry various infectious agents. Therefore, it is natural that the respiratory tract used by patients is often contaminated with these infectious bacteria. From the viewpoint of patient safety, it is clear that disinfection and sterilization of the respiratory apparatus, particularly the instruments related to the breathing circuit through which the patient breathes, are particularly important. However, surprisingly, there is no respiratory system that takes these into consideration.

The present inventor pondered on this point, considering how disinfection and sterilization operations could be easily accepted by patients and healthcare professionals with essentially no resistance. , The ventilator is divided into the drive unit body housing and accessories that directly contact the patient, and the attached connection assembly can be easily disassembled and separated by means such as insertion and removal, fitting, etc. This completes a respirator that can be performed easily and reliably down to the smallest detail.

Further, according to the present invention, the housing body and the nebulizer outside the housing, and the connection to each part of the assembly including the shock wave generator are connected via sockets respectively provided in the housing and the connection assembly. And connected by a detachable tube.

By making the tube detachable at both ends in this way, the tube can be easily washed and disinfected.
It can be very effective in preventing the adverse effects of various infectious diseases commonly seen in patients with lung disease and the risk of infection.

Further, according to the present invention, the housing main body, the nebulizer outside the housing, and the connection to each part of the assembly including the shock wave generator are connected to both ends of the housing via the sockets respectively provided in the housing and the connection assembly. In a ventilator which functions by being connected by a detachable tube, each of the connected sockets and tubes is distinguished for each connection line, and is colored in different colors to be colored.

By connecting tubes of the same color to sockets of the same color, connection lines for each function can be automatically set, so that it is possible to easily assemble even a person who is using the respirator for the first time. It can be easily and definitely set when reused after washing and disinfecting, and it is possible to avoid unsightly mistakes.

Further, the present invention relates to a ventilator for performing intrapulmonary shock ventilation treatment driven only by gas pressure, which is entirely constituted by a main body housed in a housing and an assembly connected thereto. The body has a gas inlet for introducing gas, a tube and four detachable sockets, an oscillator cartridge that converts the continuous flow of introduced gas into an intermittent flow, a label meter that indicates the pressure in the lung airway. A nebulizer and a shock wave generator are arranged in a connection assembly outside the housing, a remote switch is provided in a tube connecting the shock wave generator and the nebulizer, and a lung airway pressure is monitored at a tip of the shock wave generator. The first socket is connected to a nebulizer outside the housing by a tube, and the first socket is connected to a gas inlet in the housing. The second socket is connected by a tube to a gas flow converted into an intermittent flow by an oscillator cartridge inside the housing to a shock wave generator outside the housing, and the third socket is a sign indicating the pressure in the lung airway of the housing. The meter is connected by a tube to a tube insertion port for monitoring pulmonary airway pressure at the end of the shock wave generator, and the fourth socket is connected by a tube to a remote switch to a driving gas control circuit inside the housing. It is a respirator characterized by the following.

Further, the present invention relates to an artificial respirator for performing in-pulmonary shock ventilation therapy using a shock wave generated by the operation of a shock wave generating device as an inhalation, driven by a pressurized gas. A housing having a gas inlet for introducing a gas, an oscillator cartridge for converting a continuous flow of gas into an intermittent flow inside the housing, and an outside of the housing. So,
A nebulizer that communicates with the shock wave generator and supplies mist of water or a drug therein, a meter inside the housing that communicates with an outlet of the shock wave generator to indicate a pressure in a pulmonary airway, a nebulizer and the nebulizer; The tubular body connecting the shock wave generator and the remote switch installed in the tubular body are constituent components, and a part of the gas introduced into the gas inlet of the housing is installed on the outer surface of the housing as a continuous flow. Another part of the gas introduced into the housing is guided to the nebulizer by a tube via a socket, and another part of the gas introduced into the housing is converted into an intermittent flow through an oscillator cartridge, and the tube is connected to the nebulizer through a socket provided on the outer surface of the housing. Guided to the shock wave generator, where it forms a shock flow with percussion,
On the outer surface of the housing, sockets are respectively connected to the nebulizer from the gas introduction path, the shock wave generator from the oscillator cartridge, the shock wave generator from the indicator meter, and the remote switch from the drive gas control circuit of the oscillator cartridge. The connection of the nebulizer, the shock wave generator, the remote switch, and the shock wave generator to the pulmonary airway pressure monitoring port from the socket is performed by a detachable flexible tube.

Further, according to the present invention, the shock wave generator and the nebulizer which constitute the connection assembly may include:
An artificial respirator characterized by being assembled by fitting and capable of being disassembled.

Further, according to the present invention, the lid of the nebulizer constituting the nebulizer may be formed integrally with a tubular body connecting the shock wave generator and the nebulizer, and one end of the tubular body may be formed in the shock wave generator. The other end may be open to the atmosphere and air may be introduced into the shock wave generator, or the atmosphere may be introduced into the shock wave generator by adjusting the oxygen concentration to introduce the atmosphere into the shock wave generator. You may. Here, the tubular body may be T-shaped, L-shaped, or Y-shaped. In short, the shock wave generator and the nebulizer may be assembled airtight by fitting. .

Further, in the present invention, a single pressurized gas source is used as a driving source, and in order to make the whole function well, the mechanical properties of the gas fluid are skillfully used. An orifice can be inserted into the tract to characterize this purpose.

More specifically, the present invention will be described in detail. A sliding venturi is built in a cylindrical container, and the sliding venturi reciprocates back and forth by intermittent gas. When the intermittent gas flows in, it is momentarily closed, the positive pressure gas is spontaneously jetted, and when the intermittent gas is stopped, it is momentarily opened to release the gas in the tube to the atmosphere. A shock wave generator that converts an intermittent gas flow into an intermittent shock wave by a Venturi effect having a function of releasing the pressure load by discharging to the pressurized gas as a driving source is used by the action of the shock wave generator. A ventilator that performs respiratory assistance using the intermittent shock wave generated as inspiration, the whole is composed of a main body contained in a housing and an attached assembly connected to this,
The housing has a gas inlet, and the introduced continuous flow gas is converted from a continuous flow into an intermittent flow by an oscillator cartridge installed in the housing, and then reaches the shock wave generator, where the shock wave is generated. A ventilator which is provided with at least one orifice in a gas flow path including a driving gas control circuit in a housing, and performs a function control function with a gas flow balance. It is.

That is, the present invention relates to sockets (hereinafter referred to as service sockets) provided in the above-mentioned housing, ie, an erosol socket connected to a nebulizer, a percussion socket connected to a shock wave generator, and a pulmonary airway. At least one orifice is provided in each gas flow path in the housing leading to the connected gauge socket and the remote socket connected to the remote switch, and the amount of gas flowing to each service socket is adjusted by the action of the orifice. It is an artificial respirator.

More specifically, a sliding venturi is built in a cylindrical container, and the sliding venturi reciprocates back and forth by intermittent gas, whereby the tip of the venturi tube opens and closes to the atmosphere, When the intermittent gas flows in, it is momentarily closed, and the positive pressure gas is spouted in a shock.When the intermittent gas is stopped, it is momentarily opened to release the gas in the tube to the atmosphere. A shock wave generator that converts an intermittent gas flow into an intermittent shock wave by a Venturi effect having a function of eliminating pressure load by using a pressurized gas as a drive source is used as an intermittent force generated by the operation of the shock wave generator. A ventilator that performs intrapulmonary shock ventilation therapy using inspiratory shock waves as inspiration, the whole being composed of a main body contained in a housing and an attached assembly connected thereto, Is equipped with a gas inlet for introducing gas and four sockets that can be connected to the tube, an oscillator cartridge that converts the continuous flow of introduced gas into intermittent flow, and a meter that displays lung airway pressure in the housing. It is arranged, a nebulizer and a shock wave generator are arranged outside the housing, the shock wave generator and the nebulizer are connected by a connecting pipe, a remote switch that activates an oscillator cartridge to generate an intermittent flow, The tip of the shock wave generator is provided with a tube insertion port for monitoring the pulmonary airway pressure, and the gas flow introduced into the housing is divided into two flow paths in the housing, one part of which is a continuous flow. As it is, it is connected to the nebulizer outside the housing via the first socket, and another branched part is guided to the oscillator cartridge to form an intermittent flow, and the second socket The third socket is connected to a pulmonary airway pressure indicator meter and a pulmonary airway pressure monitor insertion port at the end of the shock wave generator, and the fourth socket is The driving gas control circuit of the oscillator cartridge and the remote switch are connected to each other, and at least one gas flow path in the housing connected to the nebulizer, the shock wave generator, the insertion port for the lung airway monitor, and the remote switch outside the housing.
One orifice is provided on each
An artificial respirator characterized in that the amount of gas flowing through each socket is adjusted.

The frequency of the percussion according to the present invention is preferably 10 to 600 times per minute, preferably 20 to 400 times, more preferably 40 to 300 times, and the operating gas pressure is 15 psi. ~ 85 psi
^{(1.0kg / cm 2 ~6.0kg / cm} 2), preferably 20~80psi (1.4kg / cm ² ~5.6k
g / cm ² ), more preferably 25 to 65 psi (2.
^{0kg / cm 2 ~4.5kg / cm 2} ), it is preferable to adjust to treatment.

In order to safely carry out the treatment, the pulmonary airway pressure (wedge pressure: wedge pressure) of the patient is adjusted to 15 times.
It is desirable to perform as a ~45cmH ₂ O.

[0061]

According to the present invention, as described above, a system for maximizing the effects of a shock wave generator is constructed, and a new feature of a respirator, a pulmonary shock ventilation therapy, is established. The fluidization of the secretions in the lungs and the opening of the bronchial obstruction were successful, and the treatment efficiency of the patient was successfully improved.

[0062]

DESCRIPTION OF THE PREFERRED EMBODIMENTS The present invention will be described in more detail with reference to the following examples.

[0063]

Embodiment 1 A first embodiment of the present invention will be described in detail with reference to the circuit diagram of FIG.

In the first embodiment, the part surrounded by the dotted line on the left side of the circuit diagram is housed in the housing 53. The right part of the circuit diagram is the connection assembly 55,
Connecting tubes 71, 72, 7 outside the housing 53
The nebulizer 14, the shock wave generator 16, the remote switch 15, and the tip of the shock wave generator 16 are connected to each other by 3, 74, respectively.

First, in the casing, the respiratory gas introduced from the respiratory gas inlet 1 is filtered to remove impurities by the filter 2, and a part of the respiratory gas is connected to the nebulizer 14 via the master switch 5 via the orifice 64. Eroso
To the nebulizer 14 through the detachable tube 71, and the mist containing water or chemical atomized here is guided to the shock wave generator 16.

A part of the continuous flow from the master switch 5 is adjusted to a desired pressure by the pressure reducing valve 3 installed in the line and guided to the oscillator cartridge 6. The set pressure is displayed on the external display 4 via the orifice 61. The gas flow changed to the intermittent flow by the oscillator cartridge 6 reaches the percussion socket 11 through the orifice 62 of the intermittent flow circuit (A), and is connected to the shock wave generator 16 by the tube 72 therefrom. In the shock wave generator 16, the spray gas from the nebulizer 14 joins with the spray gas, and by the action of the sliding venturi 39, the shock wave is converted into a shock wave and reaches the mouthpiece 17 connected to the mouth of the patient.

On the other hand, the port 4 in front of the mouse piece 17
From 1 through the tube 74 to the inside of the housing through the gauge socket 13, the airway pressure gauge 9 installed in the housing via the orifice 66 is used to monitor and display the lung airway pressure.

On the other hand, the remote switch 15 reaches the remote socket 12 via the tube 73, is connected to the driving gas control circuit (B) via the adjustment orifice 65, and presses the remote switch 15. The drive gas control circuit (B) is depressurized, the oscillator cartridge 6 is activated, and the intermittent flow of intake gas is supplied from the intermittent flow circuit (A) to the shock wave generator 16, The shock wave generated here is supplied to the patient from the mouthpiece 17. When the remote switch 15 is released, the air opening in the remote switch 15 is closed, the drive gas control circuit (B) is boosted, the oscillator cartridge 6 is stopped, and the intermittent intake gas is also stopped. That is, the shock flow is provided to the patient only while the remote switch 17 is pressed, so that it functions extremely safely.

In this embodiment, a bypass circuit 18 is formed to connect a continuous flow circuit from the pressure reducing valve 3 to the oscillator cartridge 6 and an intermittent flow circuit (A) of the intake gas from the oscillator cartridge 6 to the shock wave generator 16. The circuit 18 is provided with a manual button 8 (a circuit is opened by pressing the button, and a continuous flow flows through the shock wave generator 16), and a continuous jet flow or a manual intermittent flow can be provided as necessary.

In this embodiment, the pressure is set by the pressure reducing valve 3 in the line, and the frequency of the oscillator cartridge 6 is adjusted by the frequency adjusting meter 7 of the driving gas control circuit (B). Can be introduced into the patient's lungs, and the water or drug atomized by the nebulizer 14 can be introduced into the patient's lungs by being put on a shock wave, and the patient with respiratory failure can be rescued.

[0071]

Embodiment 2 A second embodiment of the present invention will be described in detail with reference to the circuit diagram of FIG.

In the second embodiment, the portion enclosed by the dotted line on the left side of the circuit diagram is housed in the housing 53. The part to the right of the dotted line is the connecting assembly 55
In the outside of the housing 53, the connecting tubes 71, 7
The nebulizer 14, the shock wave generator 16, the remote switch 15, and the tip of the shock wave generator 16 are respectively connected by 2, 73, and 74.

First, in the case, the respiratory gas introduced from the respiratory gas inlet 1 is filtered by a filter 2 to remove impurities, and a part of the respiratory gas is adjusted by an erosol generation adjusting orifice 2.
Erosole socket 1 adjusted to the desired continuous flow rate in 2
When the water or the chemical reaches zero, the water or the chemical atomized through the detachable tube 71 and the nebulizer 14 is guided to the shock wave generator 16.

A part of the continuous flow introduced from the breathing gas inlet 1 is adjusted to a desired pressure by a pressure reducing valve 2 installed in the line, and the set pressure is sent to an external display 4 via an orifice 61. Is displayed. The continuous flow adjusted to a constant pressure is led to the oscillator cartridge 6 via the master switch 5. The continuous flow introduced into the oscillator cartridge 6 is supplied to the driving gas control circuit (B),
Time check valve 27, balance orifice 62,
The flow is converted into a desired intermittent flow by the setting of the respiratory time adjuster 19 and the frequency adjusting meter 7, and the flow rate is adjusted by the respiratory flow adjuster 20 of the intermittent flow circuit (A) to reach the percussion socket 11. It is connected to a generator 16. In the shock wave generator 16, the gas mixes with the spray gas from the nebulizer 14, and by the action of the sliding venturi, reaches a mouthpiece 17 which forms a shock wave and is connected to the mouth of the patient.

On the other hand, the port 4 in front of the mouse piece 17
From 1 to the gauge socket 13 via the tube 74, the airway pressure gauge 9 installed in the housing 53 via the orifice 64 monitors and displays the lung airway pressure.

On the other hand, the remote switch 15
3 and connected to the driving gas control circuit (B) via the adjusting orifice 65, and when the remote switch 15 is pressed, the opening of the remote switch 15 to the atmosphere is opened and the oscillator cartridge 6 is opened. Is operated and the intermittent flow of inspired gas is supplied from the intermittent flow circuit (A) to the shock wave generator 16, where it becomes a shock wave and is supplied from the mouthpiece 17 to the patient. When the remote switch 15 is released, the air opening in the remote switch 15 is closed, the drive gas control circuit (B) is boosted, the oscillator cartridge 6 is stopped, and the intermittent intake gas is also stopped. That is, the shock flow is provided to the patient only during the period in which the remote switch 15 is pressed, so that it functions extremely safely.

In this embodiment, a bypass circuit 18 is formed to connect a continuous flow circuit from the pressure reducing valve 3 to the oscillator cartridge 6 and an intermittent flow circuit (A) of the intake gas from the oscillator cartridge 6 to the shock wave generator 16. The circuit 18 is provided with a manual button 8 (when pressed, the circuit opens and a continuous flow flows in the shock wave generator 16), and a continuous jet flow or a manual intermittent flow can be generated as necessary.

In this embodiment, a bypass circuit 23 is formed between the continuous flow circuit extending from the pressure reducing valve 3 and the intermittent flow circuit (A) of the intake gas from the oscillator cartridge 6 to the shock wave generator 16. A CPAP (persistent positive airway pressure) regulator 21 is provided, and a circuit leading to the airway pressure gauge 9 is connected to the pressure detecting section of the CPAP regulator 21 to provide a function of continuously and constantly adjusting the positive airway pressure. doing.

[0079]

Embodiment 3 The third embodiment is essentially equivalent to the first embodiment. However, in order to increase the simplicity and realize the reduction in weight, portability, and miniaturization, the third embodiment is modified. A part of the configuration included in the housing is included in the connection assembly side.

The third embodiment will be described with reference to the circuit diagram of FIG. In the same figure, a portion surrounded by a dotted frame is outside the housing 53 as a connection assembly 55.

In this embodiment, the manual button 8 and the master switch 5 of the first embodiment are omitted, and the pressure reducing valve 3,
Except that the external gas pressure indicator 4 is arranged outside the housing 53, it is essentially equivalent to the first embodiment.

FIG. 5 specifically illustrates one example of the connection assembly 55 in the circuit diagram of the first embodiment. In this example, an assembly 55 connected to a housing (not shown) by connecting tubes 71, 72, 73, 74 is shown, and the shock wave generator 16 and the nebulizer 14 are integrated with the T-shaped connecting tube 33. The assembled state is shown in FIG.

The remote switch 15 is connected to the shock wave generator 1
It is provided at the lower left part of a T-shaped connecting pipe 33 interposed between 6 and the nebulizer 14. The switch 15 is usually a spring and the circuit is closed to the atmosphere. The switch 15 is opened to the atmosphere only while the switch is pressed, and the circuit connected to the switch is depressurized and the inside of the housing (not shown; circuit diagram of the first embodiment) (See Reference). When the hand is released from the remote switch 15, the circuit is instantaneously closed to the atmosphere by the force of the spring, and the operation of the oscillator is stopped.

FIG. 6 illustrates an exploded state of the assembly 55. In this example, the T-shaped connecting pipe 33 is used.
Is formed integrally with the lid of the nebulizer 14. These can be easily and airtightly assembled as shown in FIG. 5 by fitting.

What is important here is that the assembly is held in a small size so that a person can hold the assembly in one hand and push the remote switch 15 with, for example, the thumb of the hand. As shown in FIG. 6, the maximum diameter of the container of the nebulizer 14 is 47 mm. In this embodiment, the nebulizer 14 is used.
The shortest distance from the lid to the remote switch 15 is 8m
m, the remote switch 15 from the lid of the nebulizer 14
Is 16 mm. The distance to the remote switch 15 is thus set to the nebulizer 14.
The remote switch 15 can be pressed using the thumb of the hand holding the key. Such a small assembly allows a user, for example, a patient, to perform a breathing operation by himself with one hand.

FIG. 7 is essentially the same as that shown in FIG. 6, but differs in the manner of connection shown below.

That is, FIG. 7 shows an exploded state (the size is slightly exaggerated for easy understanding). The T-shaped connecting pipe 33 is integrated with the lid of the nebulizer 14. It is not molded, and the T-shaped connecting pipe 33 is provided with the remote switch 15 and is independent, and the shock wave generator 16, the T-shaped connecting pipe 33, the lid of the nebulizer 14, and the independent bodies of the nebulizer 14 are separately formed. The fitting makes it easy and airtight to be assembled as shown in FIG. In this embodiment, as shown in FIG. 7, the size of the assembly is 50 mm in the maximum diameter of the container of the nebulizer 14 in the present embodiment. The distance to the center of the remote switch 15 is 20 mm. By determining the size in this way, a user, for example, a patient can perform a breathing operation by himself with one hand.

The circuit diagram of the first embodiment shown in FIG. 1 will be described below in more detail.

The connecting assembly 55 is outside the housing 33, and the nebulizer 14, the shock wave generator 16, the remote switch 15, and the shock wave generator 16 are connected by connecting tubes 71, 72, 73, 74, respectively.

First, in the housing 53, after the respiratory gas introduced from the respiratory gas inlet 1 is filtered by the filter 2 to remove impurities, a part thereof is connected to the nebulizer 14 via the master switch 5 and the orifice 64. The mist containing water or chemicals is led to the shock wave generator 16 through the detachable tube 71 to the nebulizer 14.

A part of the continuous flow from the master switch 5 is adjusted to a desired pressure by the pressure reducing valve 3 installed in the line, and is guided to the oscillator cartridge 6. The set pressure is displayed on the external display 4 via the orifice 61. The gas flow changed into an intermittent flow by the oscillator cartridge 6 reaches the percussion socket 11 through the orifice 62, and is connected to the shock wave generator 16 by a tube 72. In the shock wave generator 16, the sliding venturi 3
By the action of 9, a shock wave is reached to the mouthpiece 17 which is connected to the mouth of the patient.

On the other hand, the port 4 in front of the mouse piece 17
From 1 through the tube 74 to the inside of the housing through the gauge socket 13, the airway pressure gauge 9 installed in the housing via the orifice 66 is used to monitor and display the lung airway pressure.

On the other hand, the remote switch 15 reaches the remote socket 12 via the tube 73 and is connected to the driving gas control circuit (B) via the adjusting orifice 65. When the remote switch 15 is pressed, the atmosphere in the remote switch 15 is changed. The driving gas control circuit (B) depressurizes moderately, which triggers the oscillator cartridge 6 to drive the intermittent shock wave from the mouthpiece 17 to the patient. When the remote switch 15 is released, the air opening in the remote switch 15 is closed, the drive gas control circuit (B) is boosted, the operation of the oscillator cartridge 6 is stopped, and the intermittent intake gas is also stopped. That is, the intermittent shock flow is provided to the patient only during the period in which the remote switch 17 is pressed, so that it functions extremely safely. In this example, the continuous flow circuit from the pressure reducing valve 3 to the oscillator cartridge 6 and the oscillator cartridge 6
A bypass circuit 18 is formed to connect the intermittent flow circuit (A) of the intake gas from the gas to the shock wave generator 16, and the manual button 8 (pressing the button opens the circuit to allow the continuous flow to flow through the shock wave generator 16. ) Can be provided as a continuous jet flow or a manual intermittent flow as required.

In this embodiment, the pressure is set by the pressure reducing valve 3 in the line, and the frequency of the oscillator cartridge 6 is adjusted by the frequency adjusting meter 7 of the driving gas control circuit (B). Can be guided to the lungs of the patient, and the water or the drug atomized by the nebulizer 14 is introduced into the lungs of the patient by placing it on a shock wave.

In the present embodiment, a large number of orifices are arranged in the circuit in the housing 53 as described above, and the flow balance is skillfully maintained. Orifice 61 (0.013 orifice)
Is provided in front of the external display 4 so as to protect the external display 4 and accurately monitor the supply pressure. Oscillator cartridge 6 and percussion socket 1
A load orifice 62 (0.060 orifice) is disposed in the intermittent flow circuit (A) connecting the oscillator 1 and the drive gas control circuit (B) connecting the oscillator cartridge 6 and the frequency adjustment meter 7 in order to prevent excessive intermittent flow. Is a balance orifice 63 (0. 0) having a smaller diameter than the load orifice 62.
018 orifices) to balance the supply of gas necessary to control the function of the oscillator cartridge 6.

The circuit from the pressure reducing valve 3 in the line to the erotic socket 10 has an orifice 64 (0.024
An orifice is inserted so that a continuous flow gas required for spraying the nebulizer 14 can be supplied. By setting the diameter of the orifice in this way, a favorable balance between the amount of spray generated from the nebulizer 14 and the intermittent flow from the oscillator cartridge 6 is achieved,
The mixture is supplied to the shock wave generator 16 and mixed. Remote socket 1 connected to remote switch (15: thumb button)
An orifice 65 of a variable adjustable orifice diameter is disposed between the drive gas control circuit 3 and the driving gas control circuit (B). The orifice diameter has a function of driving or stopping the oscillator cartridge 6 when the remote switch 15 is pressed or released. Is set to work effectively.

An orifice 66 (0.013 orifice) is provided between the lung airway pressure gauge 9 and the gauge socket 13 to protect and accurately display the lung airway pressure gauge 9. It enables measurement of internal pressure. As illustrated in this example, the ventilator functions precisely with a single high-pressure gas source as a drive source by arranging orifices in the circuit inside the housing and balancing the entire flow.

The mechanism of shock wave generation when the remote switch 15 is pressed will be described. When the remote switch 15 is pressed, the driving gas control circuit (B) is depressurized.
The on-off valve connected to the diaphragm in the oscillator cartridge 6 opens, and gas is ejected. Most of the ejected gas reaches the shock wave generator 16 through the large-diameter orifice 62 (0.06 orifice), through the intermittent flow circuit (A). The drive gas control circuit (B) has a balance orifice 63 (0 .0) having a smaller diameter than the load orifice 62.
Due to the action of the orifice (018 orifice) and the orifice 65 of the variable adjustment type, a small amount of gas flows and the pressure rises instantaneously, the on-off valve connected to the diaphragm in the oscillator cartridge 6 closes, and gas blowing stops. The time check valve closes in a short time, the gas in the drive gas control circuit (B) is released to the atmosphere, and the pressure is reduced again. After a time corresponding to the setting of the frequency adjustment meter 7, the valve in the oscillator cartridge 6 opens. Gas gushes. Thereafter, the intermittent flow is supplied to the shock wave generator 16 by this repetition, and an intermittent shock wave of a desired frequency is generated. That is, it is understood that the flow rates are skillfully balanced by the action of the orifices in the gas circuit system including the driving gas control circuit (B), and precise control is possible despite a single gas source. Let's do it.

Further, the circuit diagram of the second embodiment shown in FIG. 2 will be described in more detail.

The connecting assembly 55 is provided outside the housing 53, and the nebulizer 14, the shock wave generator 16, the remote switch 15 and the shock wave generator 16 are connected by connecting tubes 71, 72, 73 and 74, respectively.

First, the casing 53 removes impurities from the breathing gas introduced from the breathing gas inlet 1 by the filter 2, and a part of the impurities is removed by the erosol generation variable adjustment orifice 22 at a desired continuous flow rate. Is adjusted to reach the aerosol socket 10 and through the detachable tube 71 to the nebulizer 14, where the atomized water or chemical is guided to the shock wave generator 16.

A part of the continuous flow introduced from the breathing gas inlet 1 is adjusted to a desired pressure by the pressure reducing valve 3 installed in the line, and the set pressure is set via the orifice 61 (0.013 orifice). It is displayed on the external display 4. The continuous flow adjusted to a constant pressure is led to the oscillator cartridge 6 via the master switch 5. The continuous flow introduced into the oscillator cartridge 6 is set as desired by the setting of the driving gas control circuit (B), that is, the time check valve, the balance orifice 62 (0.024 orifice), the breathing time adjuster 19 and the frequency adjusting meter 7. Load orifice 6 converted to intermittent flow and regulating flow rate
3 (0.060 orifice) via respiratory flow regulator 2
When the flow rate is adjusted to 0, the flow reaches the percussion socket 11. The flow rate to the driving gas control circuit (B) is set so as to be in a range necessary for controlling the function of the oscillator cartridge 6.
The diameter of the orifice 63 is set. The intermittent flow is connected from the percussion socket 11 to the shock wave generator 16 by a tube 72. In the shock wave generator 16, the sliding venturi 39 acts as a shock wave to reach the mouthpiece 17 connected to the patient's mouth.

On the other hand, the port 4 in front of the mouse piece 17
A gauge socket 13 is connected to the housing 53 by a tube 74. The circuit between the socket 13 and the airway pressure gauge 9 has an orifice 64 for protecting the gauge.
(0.013 orifice) is provided and the pulmonary airway pressure is monitored and displayed.

On the other hand, the remote switch 15 reaches the remote socket 12 via the tube 73, is connected to the drive gas control circuit (B) via the adjusting orifice 65 (0.018 orifice), and presses the remote switch 15 to The opening is open and the oscillator cartridge 6
Is activated and the intermittent intake gas is supplied to the shock wave generator 1
6 and is supplied to the patient from the mouthpiece 17 as a shock wave. When the remote switch 15 is released, the air opening in the remote switch 15 is closed, the drive gas control circuit (B) is boosted, the oscillator cartridge 6 is stopped, and the intermittent intake gas is also stopped. That is, the shock flow is provided to the patient only during the period in which the remote switch 15 is pressed, so that it functions extremely safely. The mechanism by which the shock wave is generated by pressing the remote switch 15 is the same as that described above, and it will be understood that the present ventilator functions by the orifice flow balance.

In this embodiment, a bypass circuit 18 is formed to connect a continuous flow circuit from the pressure reducing valve 3 to the oscillator cartridge 6 and an intermittent flow circuit (A) of the intake gas from the oscillator cartridge 6 to the shock wave generator 16. The circuit is provided with a manual button 8 (when pressed, the circuit opens and a continuous flow flows through the shock wave generator 16), and a continuous jet flow or a manual intermittent flow can be provided as necessary. Circuit 18 has a limiting orifice 66
(0.040 orifice) is inserted to balance the flow so that a large amount of gas does not flow more than necessary.

In this embodiment, a bypass circuit 23 is formed between the continuous flow circuit extending from the pressure reducing valve 3 and the intermittent flow circuit (A) of the intake gas from the oscillator cartridge 6 to the shock wave generator 16. A CPAP (persistent positive airway pressure) regulator 21 is provided, and a circuit leading to the airway pressure gauge 9 is connected to the pressure detecting section of the CPAP regulator 21 to provide a function of continuously and constantly adjusting the positive airway pressure. doing.

As described above in detail, various kinds of orifices are arranged in the circuit in the housing to balance the flow rate, and the whole including the function of the remote switch 15 is made to function organically, and a single pressurized gas is used. We have provided a ventilator that can be operated precisely at the source.

A more effective embodiment of the present invention will be described in detail with reference to the circuit diagram of the first embodiment shown in FIG. 1 and FIG.

This embodiment is different from the first embodiment in that each socket and each detachable tube are colored in different colors, and are color-coded for each connection line system, so that they can be easily handled without errors during disassembly and assembly. Specifically, the aerosol socket 10 of the aerosol line, the connection tube 71 and the socket portion of the nebulizer 14 are “yellow”, the percussion socket 11 which is an intermittent flow percussion line, the connection tube 72 and the inlet of the shock wave generator 16. The socket part is “white”, the remote line remote socket 12 and the connection tube 73 and the socket mounting part of the remote switch 15 are “green”, the lung airway pressure monitor line gauge socket 13 and the connection tube 74 and the mouthpiece 17 front port 41. Section is colored “red” and used. And the convenience of and during sterilization.

[0110]

The present invention makes full use of the shock wave generator previously devised, applies it to a ventilator, and uses the air hammer effect of percussion to fluidize secretions in the lungs. It has succeeded in creating a revolutionary treatment that can be referred to as intrapulmonary shock ventilation (IPV), and brings a great gospel to patients.

[Brief description of the drawings]

FIG. 1 is an overall circuit diagram of a ventilator according to a first embodiment of the present invention.

FIG. 2 is an overall circuit diagram of a ventilator according to a second embodiment of the present invention.

FIG. 3 is an overall circuit diagram of a ventilator according to a third embodiment of the present invention.

FIG. 4 is a structural view of a shock wave generator used for a ventilator according to the present invention, and (A) is a cross-sectional view showing a state before operation. (B) is a sectional view showing a state after the operation.

FIG. 5 shows a connecting assembly (shock wave generator, nebulizer, T-shaped connecting pipe,
FIG. 3 is an assembly view showing an example of a connection tube and the like).

FIG. 6 is an exploded view of the connection assembly shown in FIG. 5;

FIG. 7 shows a connecting assembly (shock wave generator, nebulizer, T-shaped connecting pipe,
It is an exploded view which shows an example of a connection tube.

FIG. 8 is a schematic diagram showing an outline of a jet flow generating mechanism.

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 Respiratory gas inlet 6 Oscillator cartridge 9 Airway pressure gauge 10 Service socket 11 Service socket 12 Service socket 13 Service socket 14 Nebulizer 15 Remote switch 16 Shock wave generator 33 Connection pipe (T-connection pipe) 39 Sliding venturi 53 Housing 55 Connection Assembly 61 Orifice 62 Orifice 63 Orifice 64 Orifice 65 Orifice 66 Orifice 67 Orifice 68 Orifice 71 Tube 72 Tube 73 Tube 74 Tube

Claims (1)

[Claims] A sliding venturi is built in a cylindrical container, and the sliding venturi repeatedly reciprocates back and forth by intermittent gas, whereby the tip of the sliding venturi opens and closes to the atmosphere, and the intermittent gas is removed. When the gas flows in, it is closed momentarily, the positive pressure gas is spouted in a shock, and when the intermittent gas is stopped, it is momentarily opened, releasing the gas in the sliding venturi to the atmosphere and eliminating the pressure load. A ventilator using a shock wave generator that converts an intermittent gas flow into an intermittent shock wave by a Venturi effect having a function of performing the operation is driven by a pressurized gas of 1.0 to 6.0 kg / cm ^2. And
A respirator comprising: a continuous flow from a gas source directed to an oscillator; and an intermittent gas flow generated by the continuous flow is directed to the shock wave generator to generate an intermittent impulsive breathing gas.