JPH0427867B2 - - Google Patents

Description

DETAILED DESCRIPTION OF THE INVENTION The present invention provides a respiratory apparatus,
More particularly, it relates to a complete portable breathing apparatus that can be used as a ventilator or resuscitator for a single patient for a limited period of time.

Although various types of breathing devices are known, the present invention relates to devices that are commonly referred to as resuscitation devices and/or ventilators, depending on their intended use.

A resuscitation device is defined herein as a device utilized to initiate breathing in a person who has stopped breathing. Similarly, a ventilator is defined as a positive pressure device other than a resuscitator that is utilized to assist in ventilation of the lungs.

Most known devices of this type have been developed for use within hospitals. It is powered by electricity from the hospital's power supply and is designed to utilize the hospital's oxygen supply system.

Some portable resuscitation devices have been known in the past, but since these devices usually use oxygen cylinders, they have the drawback of being heavy compared to their oxygen supply capacity. Additionally, devices that use bottled oxygen have a relatively short shelf life compared to devices that use chemical oxygen generators.
Therefore, it would be desirable to develop a portable resuscitation device that has an acceptable weight to oxygen delivery ratio and a relatively long shelf life.

Known portable resuscitation devices are designed to operate only in a fixed periodic mode. That is, a fixed amount of air and oxygen mixture is forced into the patient's lungs for a fixed period of time, and then the air and oxygen mixture is allowed to be expelled for another fixed period of time. ing. This time is selected to approximate the normal breathing cycle.

Known portable ventilation devices can only operate on demand cycles. That is, each inspiratory phase of breathing is initiated by the patient's inspiratory effect. Demand mode ventilators are not suitable for use as resuscitation equipment. This is because in this case the patient cannot trigger the operation of the device.

Similarly, limited cycle resuscitation devices are used as ventilation devices.
It is also undesirable to use it on patients who have started breathing on their own. This is because it is harmful if the breathing cycle does not match the physiological needs of the patient.

It is therefore possible to develop a portable device that can operate as a ventilator or as a resuscitator and that under normal conditions operates in a timed cycle mode, which cycle can be overcome by the patient's inhalation or exhalation movements. desired.

One object of the present invention is to provide a portable breathing device that overcomes the drawbacks of previously known devices.

More particularly, the object of the invention is a complete single-patient portable breathing apparatus of the type equipped with a chemical oxygen generator, which receives oxygen from the chemical oxygen generator during expiration and during inspiration. It is an object of the present invention to provide an apparatus having a pressure accumulator or acumulator adapted to supplement the oxygen supplied by a chemical oxygen generator, and having a long shelf life and satisfactory operating efficiency. .

Another object of the invention is a complete portable breathing apparatus for a single patient of the type described above, comprising a ventilator pump and a filter, the filtered air being mixed with the oxygen generated by the oxygen generator. The object of the present invention is to provide a device which makes it possible in particular to extend its operating period and which has an acceptable ratio of the weight of the device to the amount of oxygen supplied.

Another object of the invention is to provide an air-oxygen mixture to the patient for an initial limited period of time, and then to supply the patient's breathing cavity with an air-oxygen mixture for a subsequent limited period of time. To provide a complete portable single patient breathing apparatus of the type having an operating cycle that allows exhalation and allows the patient to prioritize his or her own breathing cycle over the inspiratory or expiratory cycle of the device. It is.

The illustrated embodiment will be described in detail below.

FIG. 1 shows a system diaphragm of a breathing apparatus according to one embodiment of the present invention.

The device includes a mask 10 and is attached to the patient by a head harness 12. Patient is respiratory cavity 1
4 and partially shown as trachea 16.

The breathing apparatus further includes an oxygen source 18, an air delivery means 20 and a fluid actuation control means 24. In addition to the mask 10 and the head harness 12, the air supply means 20 includes a valve means or distribution valve 22 that is arranged between the oxygen supply source 18 and the mask 10 and can switch between an exhalation position and an inhalation position, and other fluid elements. I'm here. If desired, an oxygen supply tube 25 may be provided. Valve 22 acts as a two-position flow directing means.

The oxygen supply source 18, which also acts as a power source,
Preferably chlorate candle
It consists of a chemical oxygen generator (candle). Chlorate candles are known, e.g.
Disclosed in No. 2507450. This candle emits oxygen via outlet tube 26 during its operation.

Immediately downstream of the outlet pipe 26 is a bench lily pump. The pump includes a vent lily 28 which directs the effluent gas from the chlorate candle through the jet orifice 27 and the vent lily 28.

According to the known principle, when oxygen passes through the constriction of the bench lily, its pressure decreases. This pressure drop is utilized to introduce ambient air into the inlet or suction section 33 of the bench lily 28 through the activated carbon filter 32 as indicated by arrow 30.
The purpose of filter 32 is to remove toxic or harmful substances from the surrounding air.

The filter has an inlet open to ambient air and an outlet communicating with the suction of the pump. A check valve is installed at the inlet of the filter so that the air flows as shown in arrow 3.
The flow may be made to flow only in the 0 direction.

The filtered air is mixed with oxygen downstream of the jet orifice 27, and this mixture is delivered through the outlet 33a of the pump 28. A pressure or flow control valve 34 is provided downstream of the pump to ensure that a relatively constant pressure of the mixture is provided to valve 22.

filter 32, pump 28, control means 24,
All oxygen generators are housed in the housing 8 shown by the dash-dotted line.
is housed within.

The distribution valve 22 is basically a 2-position, 3-port directional control valve that is normally held at the intake position shown in FIG. 1 by the action of a spring 35.
It is possible to switch to the exhalation position by the pressure in 6. When this valve 22 is in the illustrated intake position,
Gas from the oxygen generator is routed through valve 22, line 38, check valve 40, line 42, check valve 44, line 46 to mask 10, and then to the patient's trachea 1.
6 into the respiratory cavity 14. This flow continues until valve 22 is switched to the exhalation position by pressure in pilot tube 36.

When valve 22 is in the exhalation position, gas from the oxygen generator is directed through valve 22, line 48, check valve 50, and line 52 to an accumulator 54. When the pressure within the accumulator 54 exceeds its design level, the excess pressure is vented to the atmosphere via the relief valve 56.

Line 52 is connected to line 38 by line 51 with a compensated check valve 60. valve 60
is compensated for by the pilot tube 62, which communicates with the ambient atmosphere by a bleed tube 64.

Other fluid elements in the oxygen transfer system include a pressure compensated relief valve 66 as a positive end expiratory pressure valve, which is connected to line 4 via line 67 and pilot line 68.
2, the pipe 51 is also connected via the pilot pipe 69.
are connected to each. pilot tube 69
It also communicates with the atmosphere via a bleed pipe 70.

In FIG. 2, the positive expiratory pressure is expressed as a water pressure of 0 cm. Finally, a compensated exhalation valve is provided as a pressure compensated check valve 72, which check valve 72 is compensated by a pilot tube 74 extending from line 42. The check valve 44 and the pressure compensated check valve 72 form a compensated exhalation/inhalation valve and are typically attached to the mask at the end of the outlet tube 42.

The illustrated control means 24 is pneumatically operated and includes a fluid flip-flop 76. The inlet of this flip-flop is connected via line 78 to an oxygen source. This flip-flop is Norgren module 4FF-202.000
There is. The output of the flip-flop can be taken from either line 80 or 82. These pipes 80 and 82 are connected to throttles 81 and 83, respectively.
It communicates with the atmosphere through.

The pilot pipe 36 connects to the conduit 8 on the upstream side of the throttle 83.
2 and extends to the control valve 22. Flip-flop 76 is also provided with input control tubes 84 and 86.

As is well known, when a bistable flip-flop is subjected to pressure in control tube 84, the output changes from tube 80 to tube 82.
Move to. Similarly, this flip-flop 7
When 6 is subjected to pressure in tube 86, power is transferred from tube 82 to 80.

Input control lines 84, 86 are each connected to an associated output line 80, 82 via appropriate valving. Timing modules 88, 89 can be used as the valve mechanism, but fluid timing modules are known, such as the Norgren delay module 5.
There is a TD0214-000, which combines a fluid resistance capacitive circuit with a Sohmitt trigger and has a variable aperture on the input side.

The fluid timing module flows control fluid through a variable orifice 88 and output flow is triggered when a predetermined amount of fluid enters the modules 88,89. Thus, variable orifice 88 located between conduits 80 and 84 can be adjusted to trigger output flow after two seconds. Similarly, variable orifice 88 between conduits 82 and 86 can be adjusted to trigger output flow after 4 seconds.

By using such a timing module, the operation of the control valve 22 can be controlled. However, as previously discussed, the patient's physiological needs may differ from the time preset by the timing module. Therefore, a corresponding control means is added.

The control means 90 normally prevents flow from lines 80 to 84, but is adapted to open when the pressure exceeds a predetermined limit. The control means 90 overrides the operation of the timing module under certain circumstances, as described below.

Similar control means 92 can also be provided between conduits 82 and 86. This control means 92 is opened when the pressure in the mask falls below the pressure set by valve 66 due to the patient initiating an inspiration movement.

Control means 90, 92 are each shown as pilot operated two position two port directional control valves. Valve 90 is normally held in a closed position by a spring, but is opened when the pressure in pilot tube 94 exceeds a set point by an adjustable spring. Valve 92 is also normally held in the closed position by a spring, but when the patient begins to inhale and the pressure within the mask falls below the value determined by valve 66, this condition occurs when pilot tube 9
6,98, the valve 92 is shifted to its open position.

Although a two-position directional control valve is shown, other control means may be used, such as a monostable flip-flop connected to a suitable pressure relief valve. It is also possible to use a pneumatic logic control system instead of the control means 76, 88, 89, 90, 92.

In operation, the chlorate candle 18 is now started and the output of the fluid module is transferred to line 8.
Assume that it is on the 0 side. Distribution valve 22 is held in the position shown by a spring 35. Gas from oxygen generator 18 passes through bench lily pump 28 where it is mixed with air passing through filter 32.
The pressure of the mixture flowing out from the bench lily is controlled by the regulating valve 34.
controlled by.

As shown in Figure 2, the adjusted pressure is 35
The peak pressure in cm is the pressure delivered to the patient. However, higher pressures may be desired.

Gas from valve 34 is delivered to patient 14 via valve 22, tube 38, check valve 40, and mask 10.
This flow of gas will continue until the time set by the timing module between tubes 80 and 84 elapses, or the control means 90 is shifted to direct the gas from tubes 80 to 84.
Continue until it starts to flow. The normal expiratory time is shown in Figure 2, and similarly, the normal expiratory time is E
The normal expiratory cycle is indicated by TC.

Although the pressure to which valve 90 responds is adjustable as shown in FIG. 1, the valve normally responds to one of two conditions. That is, when the patient is about to exhale or when the patient's breathing cavity has filled to the set pressure. In either case, the oxygen and air mixture passing from the tube 38 through the check valve 40 has nowhere else to go but to the pilot tube 94, which connects the tube 42 and the controller 90, reducing the pressure in this tube 94. increase, thereby operating controller 90 to allow flow from tube 80 to tube 84 and shifting the output of fluid flip-flop 76 to tube 82. This pressure increase is shown at 95 in FIG. After this pressure increase, the following conditions occur:

First, valve 22 is switched from the illustrated position by pressure in line 36 and the output of oxygen source 18 is pumped through valve 22 and out of line 48 into accumulator 54 . This shortens the inspiration time SI and therefore the period SC. Since the output of the chlorate candle is substantially constant over a period of time, the generated oxygen must be stored or discarded if not used by the patient. The accumulator is a means for storing the oxygen produced by the oxygen generator for later use by the patient.

When valve 22 is in the exhalation position, gas from the oxygen source is routed to the accumulator under normal operating conditions, and as valve 60 is compensated via valve 62, the accumulated oxygen is removed when tube 48 is pressurized. and release air.

At the same time, the pressure in the pipes 38, 51 and the pilot pipe 64 is released to the atmosphere via the bleed pipe 70. As a result, the pressure compensated relief valve 66
lowers the pressure in the pilot tube 74 compensating the exhalation valve 72.

Meanwhile, the patient exhales air through valve 72 until positive end expiratory pressure (PEEP) is achieved. This pressure is determined by an adjustable valve 66 and is
It is variable between ~20cm. Once this pressure is reached, no more air will be exhausted from the valve 72.

Typically, exhalation is performed rapidly (within 1 second) and the remaining exhalation time (for example, 3 seconds) is a rest period before exhalation begins.

The intake operation is initiated by timing modules 88, 89 connected between tubes 82 and 86. That is, once the timing module's set time has elapsed, fluid is introduced into tube 86, shifting the output of the fluid flip-flop to tube 80 and terminating the exhalation cycle. Alternatively, control means 92 may be opened by the patient attempting to inhale, as shown by pressure drop 97 in FIG. That is, when the patient inhales, the pilot tube 9
6 falls below the pressure in pilot tube 98, valve 92 is shifted to the open position and a shortened exhalation cycle SE occurs.

When power is returned to line 80, valve 22 is shifted to the position shown in FIG. Additional oxygen and air is then introduced into the mask from the bench lily 28 and the accumulator. At this time, the pressure in line 62 is vented to the atmosphere via bleed line 64 and check valve 60 is no longer compensated by line 62, so that valve 60 is opened. Pipe 38, 51, 6
A pressure of 9 closes valve 66 and prevents gas from escaping from this valve.

By allowing the patient's natural physiological needs to drive the inspiratory/expiratory cycle, the caregiver can attend to other needs. Traditional portable air-controlled ventilation resuscitation devices cannot automatically lengthen or shorten timed inspiratory/expiratory cycles as needed and must be manually adjusted according to patient demand. .

One of the advantages of the device of the invention is that the control means are operated solely by the output of the oxygen source. In fact, the chlorate candle is very long e.g. 10
It has a reliable shelf life of years or more. Therefore, by using its output for cycling and pressure compensation of the device, a reliable breathing device with a long shelf life is obtained.

Another embodiment of the invention is shown in FIG. Although there are many differences between the embodiment of FIG. 1 and the embodiment of FIG. 3, two differences should be noted first. One is that the embodiment of FIG. 1 uses fluidic circuits for the control means 24, whereas the embodiment of FIG. 3 uses pneumatic logic control elements. Another difference lies in the location of the valve means.

In FIG. 1, the two-position valve is located downstream of the bench pump, whereas in the embodiment of FIG. 3, this valve is located upstream of the bench pump.

In FIG. 3, housing 108 also includes the various components of a single patient breathing apparatus. A head harness 11 is installed on the outside of the housing.
A mask 110 is provided to be worn on the patient by 2. The patient is shown as a respiratory cavity 114 and trachea 116.

The main components inside the housing 108 include:
There is a power supply 118, an air filter 120, a pump means 122, an accumulator 124 having an inlet/outlet line 126, a two-position flow direction control means 128, and lines interconnecting these components. These conduits will be described later.

Additionally located within the housing are primary control means for displacing the valve between a first position and a second position based on predetermined time intervals. This control means will also be described later. Furthermore, patient override control means are provided, by which the patient can override his or her exhalation or inspiration movements over the first control means. An outlet tube 130 extends from the pump means 122 to the mask 110.

When the device of the present invention is used as a portable unit, the power to operate it is supplied solely from a patient source such as a chemical oxygen generator 132, preferably a chlorate candle. A line 136 from the oxygen generator is provided with a check valve 134 and a gas filter 135, which form part of the power supply, and this oxygen supply line 136 terminates at the connection end J1.

As in the embodiment of FIG. 1, line 1 connects the outlet or supply line 136 from the oxygen generator to an external source of pneumatic oxygen at a suitable pressure, as required.
40 is provided, and a connector 138 is connected to this conduit 140.
is provided outside the housing 108, and a check valve 142 is inserted therein. tube 140
is connected to the oxygen supply pipe 136 at a connection point J2. The purpose of the check valves 134, 142 is to prevent backflow to the oxygen generator and coupling 138.

The two-position valve 128 has nine ports P11 and P1.
2, P13, P21, P22, P23, P31,
P32 and P33 are provided. When the spool 129 of the valve 128 is in the normal position shown, ports P12 and P13, P22 and P23, and P32 and P33 communicate with each other, but port P1
1, P21 and P31 are closed by a spool 129. Ports P11, P23, P3
1 is not connected to a pipe and is open to the atmosphere.

When valve 128 is shifted to the second position, port P12 is connected to port P11 and opened to the atmosphere, port P21 is connected to port P22, and port P32 is connected to port P31 and opened to the atmosphere. . Ports P13, P23, P33
is blocked internally, and port P23 is opened to the atmosphere.

Next, the pump means 122 will be explained in detail. The pump means is a bench lily pump and includes a hollow member 144 and a bench lily 146 disposed inside the hollow member 144. bench lily 146
A jet orifice 148 is provided upstream of the pump, around which the suction section 150 of the pump is surrounded.

The downstream side of the bench lily forms a discharge port 152 of the pump, and a check valve 154 and a flow control valve 156 are provided at this discharge port. The purpose of check valve 154 is to prevent backflow of gas through the pump and the purpose of control valve 156 is to regulate the flow rate of the pump.

The pump 122 includes a plurality of ports P1 to P7, and various pipes are connected to these ports. For example, a discharge pipe 130 is connected to the port P1.

Filter 120, shown schematically, is a canister or cartridge containing activated carbon and/or other components capable of filtering harmful components in the air. Filters of this type typically have an outlet screwed or otherwise secured to one port of the pump means, P4 in the illustrated example.
The filter further includes an inlet 1 with a check valve 162 capable of preventing backflow of gas through the filter.
60.

Filter 120 is disposed in a housing with its inlet 160 and check valve 162 located near a perforated wall such that atmospheric air is drawn into the filter when suction is applied to outlet 158.

power supply source 118, accumulator 124,
126, valve 128, and pump 122 are interconnected by a conduit. That is, the first supply pipe 1
64 extends from connection point J1 to port P13 of valve 128, and further from port P12 to pump 122.
It extends to port P2. Port P2 is located upstream of jet orifice 148. Thus, when valve 128 is in the position shown, first supply line 164 connects power source 118 to pump 122.
is connected to.

When valve 128 is in the other position, second supply pipe 166 connects from connection point J1 to port P2 of valve 128.
1, Accumulator connection point J3 via P22
extend to. Therefore, at this time, the second supply pipe connects the oxygen source 118 to the accumulators 124, 126. A check valve 168 is provided in the tube 166;
Gas flow from accumulator 124 through tube 166 to port P22 is blocked.

When the valve 128 is in the illustrated position, the third supply pipe 1
70 extends from the connection point J3 of the accumulator 124 to the port P33 of the valve 128, and further to the port 3
2 to port P3 of pump 122. Port P3 is the suction part 1 of the pump 122.
50.

A pressure control valve may be provided in the third supply pipe to control the output pressure of the accumulator so that the pressure of the gas sent from the accumulator to the pump does not exceed a certain value. Furthermore, a relief valve may be connected to the accumulator via connection point J3 to prevent the accumulator from accumulating oxygen above a safe pressure.

As can be seen, when the spool 129 of the two-position valve means 128 is in the first position, the second supply pipe 166 is closed. When the valve spool is shifted to the second position, the first and third supply tubes 164, 170 are occluded.

Spool 129 of valve 128 is normally held in a first position by a spring, but is shifted to a second position when the pilot tube pressure exceeds a first predetermined level. After reaching this first pressure level, the spool returns to the first position when the pressure in the pilot tube falls below a second predetermined level that is lower than the first level.

For this purpose, the valve spool has an extension 176
and a pair of spaced apart annular grooves are provided in the extension. These grooves are schematically shown as V-shaped notches 178 in the figures. A spring-loaded detent member 180 is engageable with the annular groove 178. The pressure of spring 182
1.75Kg/ ^cm2 , and the detent member 180 is placed in the groove 17.
Assuming a force of 0.75 Kg/cm ² is required to shift from 8, a force of 1.75 + 0.75 Kg/cm ² is required in the direction of the arrow to shift the valve to the second position. Therefore, a force at a first pressure level equal to the force of spring 182 plus the force required to lift detent member 180 is applied to pilot tube 18.
It is necessary to add via 6.

Similarly, in order to shift valve 128 from the second position to the first position, the pressure in tube 186 must rise to a second pressure level, i.e., the force required to lift detent member 180 out of groove 178 from the force of spring 182. It must be less than or equal to the value obtained by subtracting the force.

A pilot tube 186 extending from connection point J4 of tube 164 to valve 128 forms part of the primary control means. The pilot tube is provided with first and second delay means 188, 190. A volume chamber is provided for each delay means, and a common volume chamber 192 may be used as shown.

The functions of the first delay means 188 are as follows:
28 to ensure that the pressure in the pilot tube 186 increases slowly until it reaches the first pressure level. The time required for this can be set by also varying the adjustable aperture in the delay means.

Similarly, delay means 190 adjusts the amount of time required to vent pressure in pilot tube 186 between valve 128 and delay means 190 to atmosphere when valve 128 is in the second position. The operation of the primary control means will now be described in detail.

The primary control means establishes the inspiratory and expiratory cycles once power is initiated, but it is desirable that the patient be able to override the operation of this primary control means. For this purpose, patient priority control measures (patient
override control means).

This patient priority control means is a dump valve (dump valve).
valve) 194 and a switching valve 196. valve 196
is a 3-position 3-port directional control valve, with ports P8 and P
9, P10.

Pressure pipe 198 connects to oxygen supply pipe 136 at connection point J5
It extends from port P8 to port P8, and from port P9 to connection point J6 of pilot tube 186, respectively. Furthermore, the pilot pipe 200 and the sensor are connected to the valve 19.
6. This pilot pipe 200 is connected to the check valve 154 of the pump 122.
sensor 202 from port P5 provided downstream of
It has been extended to Additionally, a pilot pipe 204 extends from port P10 of valve 196 to dump valve 194. This tube has a bleed orifice 20
6 is provided. The switching valve 196 is normally held in the central position shown by a spring.

When a pressure drop at the discharge of pump 122 is sensed by sensor 202 via pilot tube 200, valve 196 is shifted to the left, communicating power source 118 to pilot tube 204. Similarly, when sensor 202 detects an increase in pressure at the pump discharge via pilot line 200, valve 196 is shifted to the right position, opening line 198 and piloting oxygen supply line 136 through line 198. It communicates with tube 186.

The breathing apparatus further includes a positive end expiratory pressure (PEEP) valve mechanism 208. Since this valve is well known, the details will be omitted, but this valve 208 is communicated with the discharge part of the pump via a discharge part 210 extending from port P6 to valve 208 on one side of the check valve 154, and also has a port It is connected to the pump via a pilot tube 212 extending from P7 to valve 208.

The mask device is equipped with a pressure compensated inhalation and exhalation valve 214. This valve is also known and is typically attached directly to a mask worn by the patient. valve 21
The inlet side of No. 4 is directly connected to the outlet pipe 1130.

The apparatus of FIG. 3 operates as follows. To start the device, the chemical oxygen generator is started by an actuating pin mechanism, usually by pulling a string. When the chemical oxygen generator 132 is started, it releases oxygen at a pressure of 50 psi. At startup, valves 128, 194, 1
96 is in the normal position shown. oxygen generator 132
Oxygen from the air is passed through tubes 136 and 164 to a jet orifice 148 and into a vent lily 146.

The pressure drop as the oxygen passes through the bench lily results in a pressure drop in the suction section 150 of the pump. This reduced pressure causes ambient air to be sucked in through the filter 120, and this sucked air is pumped into the pump 12.
Air enriched with oxygen in the mask 110 is mixed with the oxygen in the mask 2 and sent from the pump to the mask 110 via the inhalation exhalation valve 214. However, if there is a previous exhalation cycle, the accumulator 124 will be filled to the pressure established by the release valve 174 and the accumulator will be filled to the pressure established by the release valve 174 and
from the suction side 1 of the pump 122 via port P3.
Release at 50.

Since the pressure is relatively constant on either side of valve 208, the valve assumes the position shown and no gas is vented to the atmosphere. Pilot tube 2 of sensor 202
The pressure in 00 is the pump discharge pressure, and the pressure in sensor 2
02 is not sufficient to switch valve 196 from its central position.

Oxygen is also supplied to pilot tube 186 from connection point J4.
The pressure in the volume chamber 192 is gradually increased by passing through the variable throttle of the delay device 188, and the pressure in the pilot tube 186 is gradually increased.

When the pressure in this pilot tube 186 exceeds a first predetermined level, e.g. 2.5 kg/cm ³ , valve 1
28 is shifted to the second position. The throttle of the delay device 188 is normally set to reach the switching pressure in about 2 seconds. This time can be changed by changing the aperture of delay device 188. During this time, the pressure in pilot tube 204 leading to dump valve 194 is vented to atmosphere through orifice 206. The cycle described above can be called a time-limited intake cycle.

During a timed exhalation cycle, the spool of valve 128 is in the second position. As soon as the valve is switched, oxygen from oxygen generator 132 is sent to the accumulator through line 166. The relief valve 174 is preferably set at 0.14 Kg/cm ³ so that the accumulator supplies gas to the vent valve of the unrestricted (no pressure drop) circuit to prevent excessive pressure from building up in the system. At this time, since port P33 is closed, gas released from the accumulator is blocked by the spool. At this time, port P
A tube 164 extending from 12 to port P2 communicates with the atmosphere through port P11, thereby reducing the pressure within the downstream portion of tube 164 and within tube 186 between retarder 190 and connection point J4. let

Valve 208 is connected to the pressure upstream of check valve 154 and valve 2
The discharge side of the pump is maintained at the pressure established by the valve 208, as the gas is freely released through the variable restrictor 216 depending on the magnitude of the pressure established by the adjustable spring 218 in the valve 208. be done.
When the pressure on the discharge side of the pump drops suddenly below the pressure established during the inhalation cycle, the exhalation valve 214
releases gas into the atmosphere.

On the other hand, the pressure in the pilot tube 200 is measured by the sensor 20.
2 is not sufficient to move valve 196 from the central position. Therefore, dump valve 194 is maintained in the position shown. This allows the pilot tube 186 and the volume chamber 1 to
The pressure at 92 is gradually released through delayer 190. By varying the orifice size of delayer 190, the exhalation cycle can be set to about 4 seconds or other desired time.

When the pressure within volume chamber 192 drops to approximately 1 Kg/cm ² , spring 182 acting on the spool of valve 128 returns the spool to the position shown.

During an inspiratory cycle, when the patient attempts to override the inspiratory cycle by exhaling, the pressure compensated inspiratory-expiratory valve 214 is closed, so that the pump 122
The gas sent to the discharge end 152 of is not discharged.
As a result, pressure builds up in pilot tube 200 and sensor 202 shifts valve 196 to communicate the outlet of oxygen generator 132 to volume chamber 192 via tube 198 extending from connection point J5 to J6. As a result, the volume chamber 192 and the pilot tube 1
The pressure at 86 increases rapidly and is sufficient to shift spool 129 of valve 128 to the second position.

When the spool 129 is switched to the second position,
The gas in pipe 164 between ports P12 and P2 is vented to the atmosphere through port P11 of valve 128;
The pressure in tube 164 is reduced to ambient pressure.
When the pressure of the pump upstream of the check valve 154 decreases, the valve 208 closes the discharge chamber 15 downstream of the check valve.
2 is released to the atmosphere, the pressure in the pilot tube 200 is reduced, and the sensor 202 returns the switching valve 196 to its normal position. At this time, the volume chamber begins to release gas as in a normal exhalation cycle.

During the exhalation cycle, if the patient tries to preempt this cycle by handling the breath, pump 1
The pressure of the discharge portion 152 of No. 22 drops below atmospheric pressure. This causes sensor 202 to shift valve 196 to the left so that pipe 19 is connected to pilot pipe 204 to the dump valve.
Give pressurized oxygen via 8. This causes the dump valve to move to the other position so that the dump valve and
The pressure in the pilot tube 186 between the position valve 128 is reduced to atmospheric pressure and the spool 129 of the valve 128 is
to the other position to begin the intake cycle.

When this cycle is restarted, the pressure will increase to pump 1
22 and the valve 196 is returned to the central position. The pressure in the tube 204 is reduced by the restriction 206
The valve 194 is returned to its normal position as shown.

In the illustrated example, all of the various controllers are housed within the housing, but for example, the pressure controller 218, the manual operator 222 of the dump valve 194, etc. may be located outside the housing 108.

Various aspects of the present invention will be summarized below, but it goes without saying that the present invention is not limited to these.

(1) Automatically operates while the power source is operating in normal mode to periodically deliver filtered air and oxygen into the patient's respiratory cavity in inspiratory mode and to deliver exhaled air into the patient's respiratory cavity in exhalation mode. A complete, single-patient, portable ventilation/resuscitation device adapted to permit operation, including: a) a chemical system that releases oxygen at a pressure sufficiently high to oxygenate the patient's lungs for a period of time during operation; b. a filter having an ambient air inlet and an outlet for removing toxic or harmful contaminants from the ambient air; c. powered by oxygen from said power source; , having a suction part and a discharge part communicating with the outlet of the filter, and when driven by the power supply source, draws ambient air through the filter into the suction part and mixes it with the oxygen to form an air-fuel mixture. pump means for discharging from said outlet; d an accumulator for receiving oxygen from said chemical oxygen generator during an exhalation mode and for replenishing the oxygen supplied by said chemical oxygen generator during an inhalation mode; e an outlet tube having one end connectable to the outlet of the pump and the other end connectable to the patient; a two-position flow directing means operative to deliver oxygen to said accumulator in a second mode; g operated by oxygen released by said oxygen generator and during operation of said power supply; control means for operating said flow directing means in said first mode for a first limited period of time during an inspiratory mode and in said second mode for a second limited period of time during an expiratory mode; A device consisting of.

(2) The device of paragraph (1), wherein the filter, power source, pump means, and control means are all housed within the housing.

(3) The device includes a mask and a head harness, and the other end of the outlet pipe is connected to the mask (1)
Section equipment.

(4) The pump means includes a jet orifice through which pressurized oxygen passes and is discharged, and a vent ule disposed downstream of the jet orifice, the suction portion being disposed upstream of the vent turret, and the discharge portion The device according to item (1), which is placed downstream of the ventilate.

(5) The device according to paragraph (1), wherein the chemical oxygen generator is a chlorate candle.

(6) The control means includes a pressure sensing control means, the pressure sensing control means shifting the two-position flow directing means to the first mode when the patient begins an inspiratory effort so that the pressure to the patient is set. (1) configured to be able to switch said flow directing means to a second mode when the pressure exceeds said pressure;
Section equipment.

(7) The apparatus of paragraph (1), wherein the flow directing means is located downstream of the pump.

(8) The apparatus of paragraph (1), wherein the flow directing means is located upstream of the pump.

(9) the control means includes two displaceable valves;
The device of paragraph (1), wherein one valve is shifted during patient exhalation and the other valve is shifted during inspiration.

10. The apparatus of claim 9, wherein said control means further includes a fluidic flip-flop element having an input connected to an oxygen source.

(11) Operates automatically during operation of the power supply in normal mode to periodically deliver filtered air and oxygen into the patient's respiratory cavity in inspiratory mode and to deliver exhaled air into the patient's respiratory cavity in exhalation mode. A complete, single-patient, portable ventilation/resuscitation device adapted to permit operation, including: a) a chemical system that releases oxygen at a pressure sufficiently high to oxygenate the patient's lungs for a period of time during operation; (b) a filter having an inlet and an outlet for ambient air to remove toxic or harmful contaminants from the ambient air; (c) a suction section and a discharge section communicating with the outlet of the filter; a pump means which, when driven by the oxygen source, draws ambient air through the filter into the suction section, mixes it with the oxygen, and discharges a mixture from the discharge section; d. during exhalation; an accumulator which receives oxygen from said chemical oxygen generator and which, during inspiration, delivers accumulated oxygen to said pump means; e a conduit communicating between said oxygen generator, said pump means and said accumulator; f operatively connected to said conduit, in a first position blocking the flow of oxygen from said oxygen generator to said acumulator and in a second position preventing the flow of oxygen from said oxygen generator to said pump means; g. two-position valve means actuated by oxygen released by said oxygen generator to prevent said two-position valve means from operating in a first limited mode during operation of said power supply; primary control means operative to place the pump in the first position for a period of time and in the second position for a second limited period of time during an exhalation mode; and an outlet conduit connected to the patient at the other end.

(12) the pump means includes a check valve in the discharge portion, the check valve adapted to prevent backflow through the pump means, and further includes a positive end expiratory pressure (PEEP) valve; A portion of the PEEP valve is connected to the discharge side of the pump means downstream of the check valve, and another portion of the PEEP valve is connected to the pump means upstream of the check valve. ) device.

(13) The device according to paragraph (11), comprising a power supply source, a filter, a pump means, an accumulator, a conduit, a two-position valve means, and a primary control means within the housing.

(14) The apparatus of paragraph (13) further comprising pressure compensated inhalation/exhalation coupling valve means, said valve means being disposed in relation to said mask outside said housing.

(15) The conduit means includes first, second, and third supply pipes, the first supply pipe extending from the power supply source to the pump means, and the second supply pipe extending from the power supply source to the pump means. a third supply pipe extending from the accumulator to the pump means, the two-position valve means being connected to the first, second and third supply pipes; Item (11) wherein the second supply pipe can be shut off when in the second position, and the first and third supply pipes can be shut off when the second supply pipe is in the second position. equipment.

(16) a pilot pipe extending from the first supply pipe to the valve means downstream of the valve means, the two-position valve means being normally biased to the first position by a spring; 16. The apparatus of claim 15, wherein the apparatus is movable to a second position in response to pressure in the pilot tube exceeding a first predetermined value.

(17) A first delay means is provided in the pilot pipe, and this delay means waits until a predetermined time elapses after the pressure in the first supply pipe reaches the first predetermined pressure. , the apparatus of clause (16) operative to prevent movement of said two-position valve means from said first position to said second position.

(18) The second position valve is configured to operate the valve from the second position to the first position only after the pressure in the pilot tube has decreased below a second predetermined value that is lower than the first predetermined value. The device according to paragraph (16), which is displaceable by a spring bias to the position.

(19) The first and second
delay means are arranged, these means delaying switching of said two-position valve from one position to the other position for a predetermined time after a predetermined pressure is achieved in said first supply pipe. The device according to paragraph (18), which is made as follows.

(20) said two-position valve means is displaceable between a first and a second position in response to a change in pressure in said first supply pipe downstream of said valve means; and second delay means, which means prevent displacement of the two-position valve until a predetermined variable time has elapsed.

(12) Patient operation priority control means extending between the power source and the outlet side of the pump means and the pilot tube, the control means controlling the pressure in the outlet of the pump means due to expiratory effort of the patient. operates in response to an increase in
The device according to clause (20), configured to switch from the position to the second position.

(22) A dump valve for discharging the fluid in the pilot tube to the atmosphere is provided in the pilot tube, and the patient operation priority control means extends to the dump valve, and the pump means discharges fluid according to the patient's inspiratory effort. The device according to item (21), wherein the two-position valve means is shifted to the first position by shifting the dump valve to its exhaust position in response to negative pressure within the dump valve.

[Brief explanation of drawings]

FIG. 1 is a fluid circuit diagram showing an embodiment of the present invention;
Figure 2 shows a normal breathing cycle with an inspiratory time of 2 seconds and an expiratory time of 4 seconds, and a pressure-shortened breathing cycle that the patient has prioritized over the normal cycle to meet his physiological needs. The graph of the time curve, FIG. 3, is a fluid circuit diagram showing another embodiment of the present invention. 10,110... Mask, 12,112... Head harness, 14,114... Breathing cavity, 18,132
...oxygen supply source, 20... air supply means, 22... distribution valve,
24... Fluid operation control means, 32, 120... Filter, 54, 124... Accumulator, 122...
Pump, 128...2 position valve, 192...Volume chamber, 1
94...Dump valve, 196...Switching valve.

Claims (1)

[Scope of Claims] 1. A chemical oxygen generator that generates oxygen at a pressure sufficient to deliver oxygen to the lungs of a human being; and b. An inlet and an outlet that are open to the surrounding air. , a filter for removing toxic or harmful components from the surrounding air; c. a suction section and a discharge section that receive oxygen from the oxygen generator and are driven by the oxygen and communicate with the outlet of the filter; pump means for sucking ambient air through the filter into the suction section when driven by oxygen from an oxygen generator, mixing it with the oxygen and expelling a mixed gas from the outlet; an accumulator for receiving oxygen from a chemical oxygen generator and replenishing the oxygen supplied by the chemical oxygen generator during an inhalation mode; e one end connectable to the outlet of the pump;
a conduit system having a second end connectable to the patient; f connected to the pump and the acumulator;
a two-position flow direction control means operable to selectively deliver oxygen to the patient in a first mode and to deliver oxygen to the accumulator in a second mode; g. is thus operated to place the flow direction control means in the first mode for a first limited period of time during an inspiratory mode and to place the flow direction control means in the second mode for a second limited period of time during an expiratory mode. 1. A breathing apparatus comprising: a control means for controlling the air to be placed in the air; 2 a. a power supply consisting of a chemical oxygen generator delivering oxygen at a pressure sufficiently high to oxygenate the patient's lungs for a period of time during operation; and b. an inlet and an outlet for ambient air. , a filter for removing toxic or harmful contaminants from ambient air; c. a suction portion and a discharge portion communicating with an outlet of said filter, and when driven by said oxygen supply source, causes ambient air to pass through said filter; a pump means for sucking into the suction section, mixing it with the oxygen, and discharging the mixture from the discharge section; d receiving oxygen from the chemical oxygen generator during exhalation and discharging the accumulated oxygen during inspiration an accumulator feeding the pumping means; e a line communicating between the oxygen generator, the pumping means and the accumulator; f operatively connected to the line and in a first position connecting the oxygen generator to the accumulator a two-position valve means for blocking the flow of oxygen to the oxygen generator and in a second position blocking the flow of oxygen from the oxygen generator to the pumping means; g. the two-position valve means being in the first position during operation of the power supply for a first limited period of time during an inhalation mode and for a second limited period of time during an exhalation mode; h) an outlet conduit connected at one end to the outlet of the pump means and at the other end connected to the patient; A breathing apparatus featuring: