JPH06508766A - Fail-safe device for breathing gas supply equipment - Google Patents

Abstract

(57) [Summary] This bulletin contains application data before electronic filing, so abstract data is not recorded.

Description

[Detailed description of the invention] Fail-safe device technology for breathing gas supply equipment The present invention broadly describes the application of pulsed doses of breathing gas to a patient. The present invention relates to a fail-safe device for a breathing gas supply device that provides

More particularly, the present invention provides a method for preventing a pulsed dose delivery device of breathing gas from operating properly. Contains a fail-safe device that ensures continuous flow of breathing gas to the patient in the event of .

Background technology Administering supplemental oxygen to patients with chronic obstructive pulmonary disease and other respiratory diseases is a long-standing customary practice. Devices commonly used for oxygen administration are , into a mask placed over the patient's nose or mouth, or inserted into the patient's nostrils A constant flow of oxygen is applied at a fixed flow rate through a cannula terminating in the device (nares). supply

A constant flow device is supplied during the exhalation and rest phases of the patient's breathing cycle. The excess oxygen is wasted because the oxygen is not used. Therefore, breathing Eliminates oxygen wastage by regulating oxygen flow by turning it on and off in sync with the cycle. A device has been developed to prevent this from occurring. These devices generally detect the onset of inspiration. and relatively rapidly at the beginning of inspiration (but only for a short time during the inspiration period). It operates by delivering pulses or doses of oxygen (continuously). Ru.

Typically, the sensors and controls in such devices are electrically operated and battery powered. etc. power source is required. Additionally, the valves used to control oxygen flow are typically electrically operated. It is a type solenoid valve. If a sensor or control circuit fails or the power is interrupted, acid The supply of basic doses or doses of oxygen is stopped. If the oxygen dose stops being delivered, the patient will It can cause serious adverse effects and even be life-threatening. Therefore, Pal Low-dose oxygen supply devices typically have a have the means to do so.

Generally, pulse I oxygen devices known in the prior art come in two types viz. , a format using rate-time metering, Divided into formats that use volume-metric metering and It will be done. An example of a device for volume control is disclosed in U.S. Pat. No. 4.705.034. has been done. It was also developed by Dr. Gerald Durkan and his American Demand acid disclosed in National Patent No. 4.457.303 and No. 4.462.398 The elementary controller is of the type that controls the flow rate for one hour. This controller is city In the commercial implementation, there is a method for switching the gas supply between pulsed and continuous flow modes. A dynamic selector switch is used.

Another example of a pulse-dose oxygen delivery device using hourly flow rate control is shown in U.S. Pat. There is a Puri tan-Bennet device disclosed in , 706.664. . This device is designed to revert to conventional continuous flow operation upon interruption of power or circuit failure. It is designed to. Return to continuous flow operation is in the open position when the solenoid is deenergized. mechanically pressing an electrically actuated solenoid valve configured to move to a position; This is done by This configuration allows the solenoid to overcome mechanical pushing force and to maintain valve position. It is necessary to supply sufficient power to change the position. solenoid valve closed It remains energized while in the flow blocking position.

Changes oxygen from pulsed dose delivery mode to continuous delivery mode in case of failure or power interruption All prior art backup devices that allow changes to the mode have practical drawbacks. have. Dr. Durkan's device allows the patient to detect a malfunction and press the selector switch. Requires changing the position of the tip with the body. Puritan-Benesotho device is automatic functions, but keeps the solenoid valve mechanically pressed in the energized state. The power consumption of the device is very high.

Disclosure of invention According to the present invention, an intermittent flow device provides an emergency flow or phase supplying oxygen to a patient. For any reason other than when the supply gas is exhausted, If the intermittent flow device stops supplying the patient with a continuous flow of oxygen or other breathing gas, The methods and means for supplying the This method and means control the flow rate for one hour. It can be used in either a device or a volumetric device.

The failsafe device of the present invention has a movable piston disposed within a cylinder. and the piston is secured to one end of the cylinder by a spring or other suitable means. is elastically pressed in the direction of The force added by the breathing gas is cyclically applied to the end of the cylinder in synchronization with the cylinder operation and in the opposite direction to the suppression means. be provided. The pressure of the supplied gas is such that the piston overcomes the pressing force and increases inside the cylinder. Large enough to allow movement. Also, it is consistent with the cycle operation of the device. Accordingly, means are provided to reduce the force with which the gas pressure acts on the cylinder.

Movement of the piston to the extreme position actuates the valve means to provide a continuous controlled flow of breathing gas. supplied to the patient from the source. The pushing force acting on the piston is increased by the breathing gas. The speed at which the force is applied to the cylinder is adjusted to the applied force, and the speed at which the force is applied to the cylinder is The setting is such that it takes a predetermined time for the valve means to move and operate the valve means. The dose is Each time the patient is supplied, the device is reset and a predetermined period of time for actuation of the valve means. Just start anew.

It is therefore an object of the present invention to When such an event occurs, a continuous flow of breathing gas to the patient is required. To provide a method and means for automatically establishing a metered flow be.

Another object of the invention is to provide An object of the present invention is to provide an effective fail-safe device for a gas supply device.

Other objects of the invention will become apparent from the following description of exemplary embodiments and configurations. It will be.

Brief description of the drawing In the drawings, specific embodiments of the invention are shown.

FIG. 1 shows the configuration of a pulsed dose gas supply device equipped with a fail-safe device of the present invention. It is a block diagram showing parts.

Figure 2 shows a fail-safe system that incorporates a one-hour flow rate control type gas supply device. FIG.

Figure 3 shows a Ferre equipped with a one-hour flow rate control type gas supply device using a three-way valve. FIG. 3 is an overall schematic diagram showing the safe device in partial cross-section;

Figure 4 is a partial cross-sectional view of a fail-safe device using a double-acting volume control type device. FIG.

Figure 5 shows the overall structure of a fail-safe device using a volume control device in a partial cross-sectional view. It is a schematic diagram.

Figure 6 shows a means of using a volume control device and varying the size of the body according to the respiration rate. FIG. 6 is an overall schematic diagram showing, in partial cross-section, another embodiment of the fail-safe device provided with the device; .

FIG. 7 is an overall schematic diagram showing a modification of the embodiment of FIG. 6 in a partially sectional view.

Figure 8 shows the fail-safe device used to operate the external bypass valve. FIG. 2 is an overall schematic diagram shown in section view.

BEST MODE FOR CARRYING OUT THE INVENTION The fail-safe device of the present invention comprises a flow rate hourly pulsed dose gas supply device and a volumetric Can be used for both russ dose gas supply devices. Furthermore, the failsafe device of the present invention can be incorporated as an integral part of any type of gas supply equipment, or can be used as an additional accessory to existing units.

FIG. 1 shows that the pulsed dose gas supply device 11 is connected to the fail-safe device 12 and pressure regulator The present invention is generally illustrated in the form of a block diagram interconnected to a breathing gas source 13 with This is shown below. The gas supply device 11 is based on the above-mentioned Durka, n and Puri. It is of the one-hour flow rate control type disclosed in the U.S. patent of Tan-Benguchi et al. or the volume described in commonly assigned U.S. Pat. No. 4.705.0:34. It may also be in a controlled format.

Respiratory waste (generally oxygen) from source 13 is transferred to the supply system via conduit means 14. 11 and via conduit 15 to fail-safe device 12 .

Generally, a pulsed dose gas supply bag fill detects the onset of intention and then fills the gas supply bag. means for immediately delivering a dose of gas to the patient via cannula 16. .

Cannula 16 suitably terminates in a nasal appliance 17 that is mounted within the patient's nostril. ing. The supply source 13 is a cylinder containing high pressure oxygen or a cylinder containing liquid oxygen. A Yuwar flask may be used, or an oxygen liner may be used for installation in facilities such as hospitals. It may be fine. Between the supply device 11 and the failsafe device 12 is a patient's respiratory system. suitable for applying and removing force on the fail-safe device 12 in synchronization with the cycle. Connecting means 18 are provided. Time between successive doses delivered by the delivery device 11 If the interval exceeds a predetermined length, the failsafe device 12 A continuous flow of gas from source 13 and conduit 15 to a conduit connected to cannula 16. 19 to provide a regulated pressure greater than atmospheric pressure so that the patient can breathe. Do it like this. A flow setting orifice 20 is shown for regulating gas flow to the patient. It is provided in the conduit I9 (it may also be provided in the conduit 15).

FIG. 2 shows a particular embodiment of a dosing device according to the invention using hourly flow rate control. It is. This figure 2 shows only the gas flow path in the dosing device and does not show the entire gas flow path. The control circuit is not shown (the complete control circuit is shown, for example, in Durkan U.S. Pat. 4, 457.303). In this example, the fail-safe The housing 12 has a cylinder 21, and a piston 22 is arranged inside the cylinder 21. has been done. The piston 22 is compressed by elastic restraining means such as a spring 24. 2 is pushed towards the end 23 of the cylinder 21.

A vent hole 25 is provided at the opposite end of the cylinder 21 so that the piston 22 can When moving back and forth, gas can freely enter and leave the cylinder 21. ing.

Valve 30 is a spring return, 5-port, four-way valve with a single solenoid. The valve 3 0 functions as part of the pulsed dose gas supply device it and controls the control circuit of said device 11. The circuit operates in response to a signal generated by the circuit. Position shown (this position is energized (in the permanent position), the sensor 36 is connected via the cannula 16 and the line 37. is in fluid communication with nasal appliance 17 while oxygen from source 13 is in fluid communication with conduit 14. and a line 31 along the path passing through the valve 30 (the line 31 is provided with a check valve 32). guided by). The check valve 31 allows flow only in the direction of the arrow. It is arranged like this. Gas bypasses check valve 32 and enters bleed orifice 34 In order to allow flow into the cylinder 21 at a low bleed speed set by A bypass loop 33 is provided. The gas flowing into the cylinder 21 is The piston 22 is pushed to the right by overcoming the force in the opposite direction applied by the spring 24. do. via conduit 15 or line 14 to the source 13 and the wall of cylinder 21. The valve port 38 is in communication with the valve port 38. On the cylinder wall opposite port 38 , another valve bow 1-38a is provided. Both valve ports 38.38a are piston It is normally closed or obstructed by the ton 22.

The device operates as follows. Sensor 36 is an optional sensor capable of detecting the onset of patient volition. A suitable pneumatic/electrical sensing device. When the rise of the ego is detected, the sensor 36 generates a signal that is communicated to a control circuit (not shown) of the device for processing. . In response to the signal, a control circuit energizes a valve actuator (not shown) to actuate the valve. 30 to the biased position. In this biased position (the other position), the valve 30 is The gas flow path through is as shown on the left hand side of valve 30. i.e. the line 31 is connected to cannula 16 via valve 30, and line 14 is connected via valve 30 to cannula 16. It is connected to cannula 16 and sensor 36 is shut off. The valve 30 is injected into the patient. It remains in the other position for a period of time determined by the amount of gas applied. held. The valve actuator, or solenoid, is then deenergized, causing the valve to return to its normal state. It is returned to the deenergized position. Normally, the time the valve 30 is energized is longer than the normal time. set fairly short, which allows the gas dose to be administered during the early stages of .

Each time the device delivers a pulse dose, the pressure in cylinder 21 increases is lowered by gas flow through check valve 32, four-way valve 30, and cannula 16.

Due to this pressure release in the cylinder 2, the piston 22 is moved by the pressing force of the spring 24. and is moved toward the left end of the cylinder 21. For any reason 1. <For Luz If an event occurs in which the dose delivery device 11 stops delivering a dose, the valve 30 In the deenergized position, a bleed flow of gas flows through line 31 into cylinder 21. Try to keep going. At this point, the piston 22 has the valve port 38.38a covered. It is pushed to the right until it no longer moves. This allows gas to flow from the supply source 13 into the cylinder. continuous flow through the tube 21 and line 19 to the cannula 16 and the patient. Can be done. The flow II (flow rate) of the gas stream is regulated by a flow control orifice 30. Ru.

The time between the final dose and the creation of an emergency continuous gas flow to the patient the size of the piston 22 before opening the valve port 38.38a. It is set by adjusting the distance that 22 moves and the strength of spring 24.

When normal operation of the device is resumed, the pressure in the cylinder 21 is released. The failsafe device 12 is automatically reset and the piston 22 moves to the left. The valve port 38.38a can then be closed again.

When the patient's breathing slows, the fail-safe device 12 activates to increase the dose. The height is increased marginally. This effect usually occurs at a dose of depending on the volume of gas in the cylinder 21 that is delivered to the patient. When breathing rate decreases This effect of increasing the dose size is due to the fact that cavantane steel is used in parallel with the cylinder 21. It can be further increased by providing a chamber 39. capacitance channel The size of the bar 39 also affects the time interval between the final dose and the formation of a continuous gas flow to the patient. give a sound.

The illustrated valve arrangement protects the sensor 36 from pressure surges of the supplied gas pulses. .

For devices that do not require protection of the sensor 36, the 5-port valve shown can be replaced with a 4-port type. Can be replaced with a reverse four-way valve.

FIG. 3 shows another embodiment of the fail-safe device of the present invention. This fruit The embodiment temporarily connects the source 13 to the cannula 16 during the pulse dose delivery time interval. Emergency flow to the patient provided by a limited flow intermittent flow device using an interlocking three-way valve In other words, a fail-safe flow is formed.

Similar to the embodiment of FIG. 2, oxygen or other breathing gas 13 is supplied at a regulated pressure above atmospheric pressure. Supplied. A line 14 connects the source 13 and one side of the flow control valve 41. On the other hand, the branch line 15 connects to the valve port on the cylindrical side wall of the fail-safe unit 12. route 38. The failsafe unit 12 is the same as shown in FIG. It has a cylinder 21 that accommodates a piston 22. Piston 22 is pressed in the direction of the cylinder end 23 by the force of the pressing spring 24. Figure 2 Unlike the embodiment, the opposite end of the cylinder 21 is not vented, but instead , is directly connected to line 19, and connects the inside of cylinder 21 and cannula I6. It communicates between. Regulates gas flow to the patient when the device is in its continuous flow mode flow setting orifice 20 is provided in line 15 instead of line 19. However, the reason will become clear later.

This embodiment of the invention operates as follows. Valve 4I has a single solenoid This is a spring return type three-way valve, and the position shown is the normal position, i.e., not energized. position (neutralization position). In this valve position, sensor 39 is connected to valve 41 and cannula. It communicates directly with the open end of the nasal appliance 17 via the thread 16. Sensor 39 indicates the start of self-will. Upon detection of a pressure drop indicative of the Occur. In response to the signal, the control circuit energizes the valve 41, as shown in the right half of the valve diagram. Then, the valve 41 is moved to the other position. In this other position, that is, the biased position, Valve 41 isolates sensor 39 from the device and connects supply line 14 and cannula 6. Concatenate. This connection allows the desired gas dose to be delivered via cannula 16 and nasal appliance 17. and is maintained for a predetermined period of time sufficient to supply the patient. After this, the valve 41 is deenergized. and the valve 41 returns to its normal position.

When a pulse of oxygen or other gas is delivered to the patient via cannula 16, At any time, line 4 leads to space 45 in cylinder 21 via check valve 44. A small gas pulse is also introduced at 3. The space 45 resists the force of the pressing spring 24 and gas pressure (this gas pressure is applied to the connection between line 19 and cannula 16). Due to the Venturi effect of the gas volume rushing through the connection 46, Capacity/cannulation suture for storing cannula pressure (momentarily lower than cannula pressure) functions as a member. To maximize the Venturi effect, set the flow rate orifice 2. Preferably, 0 is placed in line 15 rather than line 19.

The pressure exerted by the spring 24 on the gas in the space 45 via the piston 22 is cannula 1 through bypass line 47 and bleed orifice 48 during the Generate a gentle bleed flow that returns to 6. The gas in the space 45 flows out (bleat ), the piston 22 or the end 23 of the cylinder 21 gradually moves to the left. move towards As long as the gas pulse continues to be delivered to the patient, the gas in space 45 will continue to change. Press the piston 22 to the right repeatedly with each dispensed dose. Fill between gas doses. After a period of time has elapsed, the gas in the space 45 is exhausted, and the piston 22 is thereby Move to the left and approach the cylinder end 23. When approaching the cylinder end 23, Piston 22 opens port 38 in the side wall of cylinder 21, thereby allowing access to the patient. An emergency fail-safe flow of gas is initiated. When port 38 is opened, gas , from source 13 through line 14.15 and port 38 to line 19 and crab. It flows into the urea 16 and is supplied to the patient. Of course, the flow rate of the waste flow is determined by the flow I setting. Adjustment is made by a swivel chair 20. Between the delivery of the final gas pulse and the start of the emergency flow The time is /volume of space 45 in cylinder 21, size of bleed orifice 48 Alternatively, it can be changed by changing either the force of the spring 24. Gas pulse supply When restarting, the device automatically returns to intermittent flow.

FIG. 4 shows the format disclosed in applicant's U.S. Pat. No. 4.705.034. The flap of the present invention is configured for use in a double-acting volumetric displacer. This indicates a fail-safe device. In this configuration, the oxygen supply is similar to the previous example. A source 13 is provided, which source I3 connects it to one port of the flow control valve 51. It is equipped with a line 14 that connects to the port. The branch line 15 is connected to the line 14, Fail-safe device] 2 is connected to the port 52 provided on the wall of the cylinder 21 ing. The volumetric displacer 54 has a closed cylinder 55, which A piston 56 is arranged within the cylinder 55 . The piston 56 is one part of the cylinder 55. It freely reciprocates back and forth between one end 57 and the other end 58. cylinder 55 A conduit 59 leads into the interior of the cylinder 55 through an end 57 of the conduit 5. 9 communicates with the port of the valve 5I. Through the end 58 of the cylinder 55 a similar A conduit 60 extends and communicates with the second port of valve 51.

After the device has operated for one full cycle, the valve 51 in the position shown is The oxygen supply source 13 and the inside of the cylinder 55 are connected through the line 14, the valve 51 and the line 59. Concatenate directly. The syringe is configured such that a dose of oxygen can be delivered to the patient via the nasal device 17. The other end 58 of the cylinder 55 is in open communication with the cannula 16 via a line 60 and a valve 51. I'm passing through. Since the oxygen supplied through line 59 is at high pressure, piston 5 6 in the direction of the end 58 of the cylinder 55 to drain the oxygen in the end 58 to the line 60. Push it out through. When the piston 56 reaches the end 58 of the cylinder 55, the piston The ton 56 stops and the free space or cylinder volume on the left side of the piston 56 becomes It is filled with oxygen at a pressure equal to the pressure of the source 13.

At the midpoint between the ends 57, 58 of the cylinder 55, the walls of the cylinder 55 A port 62 is provided. As shown, port 62 is connected to conduit means 63. and is connected to the inside of the cylinder 21 of the fail-safe device 12. to conduit 63 is provided with a check valve 64 so that flow is formed only in the direction of the arrow. There is. Further, a bypass line 65 is provided to bypass the check valve 64, and the bypass line 65 is provided to bypass the check valve 64. Flow within pass line 65 is restricted by bleed orifice 66. Now , the piston 56 of the displacer 54 passes through the midpoint of the cylinder 55 and reaches the end 5. 8, port 62 is opened and the acid at essentially the pressure of source 13 is released. exposed in plain sight. This allows the bleed orifice 66 of the bypass line 65 to Gas flows through and flows into the fool-safe cylinder 21 . This gas flow As a result, the piston 22 of the failsafe device 12 resists the resistance force of the spring 24. moved to the right. At the end of the piston 56 or cylinder 55 of the displacer 54 Bleed flow through orifice 66 continues for some time.

Valve 51 has a sensor and valve 51 in its two positions (one position is the position shown). , the other position is the position in the right half of the valve drawing). Controlled by Movement of the valve 51 from one position to the other is restricted. It is synchronized with the onset of the patient's will by the control circuit. As shown, the other side of the valve 51 By moving to the position, the flow path is switched in the opposite direction, and line 59 and cannula 1 6 is connected, and the line 60 and the oxygen supply source 13 are connected. gas is syringe When it flows forcefully from the tube 55 to the patient via the cannula 16 and the nasal instrument 17, The pressure on the left side of the displacer piston 56 drops instantly. The check valve 64 is The pressure in the space 67 inside the cylinder 21 is transferred to the cannula via the displacer 54 and the valve 51. The piston of the fail-safe device 12 22 is also reset to the left. For some reason, displacer piston 5 6 no longer moves periodically and remains at one end 57 or the other end 58 of the cylinder 55. If this happens, the gas at the pressure of source 13 will flow out through orifice 66. Continue to push the piston 22 to the right. Eventually, the piston 22 will move sufficiently to the right. to open ports 52,53 and allow gas to flow between source 13 and cannula 16. Creates another metering path for continuous flow. Displacer 54 resumes normal operation In this case, the failsafe device 12 is depressurized and the piston 22 moves to the left. and closes ports 52,53, thereby closing the gas flow path on that side.

The flow capacity through valve 64 and line 63 is greater than the flow capacity through conduit 15. This ensures rapid depressurization of the flow control device. The illustrated valve 51 , a two-position four-way reversible valve. However, for example, U.S. Patent No. 4,705.03 Other functionally equivalent valves, such as the two three-way valve connection structure disclosed in No. 4, may also be used. It can be used satisfactorily.

FIG. 5 shows a fail-safe device of the present invention that can be used in other types of volume control devices. It shows. In this embodiment, the volumetric displacer 70 is a cylinder 72. Flow control valve 80 has a piston 71 actuated within a functionally equivalent second position. It is a three-way valve. The piston 71 operates against the spring 73 and the piston rod 7 4 is installed. The piston rod 74 has a stopper 76 and a rod end 7. 5 limits movement of the piston 71.

When flow control valve 80 is not energized (i.e., in the position shown), the supply Oxygen from source 13 is conveyed into conduit 81 through valve 80. The conduit 81 through the end 23 of the cylinder 21 of the fail-safe device 12 and into the interior of the cylinder 21; It communicates with Oxygen is supplied to the metered displacer 70 by a branch line 82. This applies pressure to the head of the piston 71. This causes the piston 71 to is pushed rearward against the force of spring 73 until rod end 75 engages stopper 76. I'll do it. At the same time, the oxygen pressure acting on the piston 22 of the device 12 causes the piston to 22 is forced to the right against the force of spring 24 and the air pressure in spring compartment 83. Ru. The pressure within the compartment 83 is maintained by a vent line 84 and a flow restricting bleed orifice 85. It is slowly lowered by the flow of air through it. While valve 80 is in the position shown, The piston 22 eventually fills the port 86 in the wall of the cylinder 21. Continue moving to the right until it opens in minutes. When port 86 is opened, source 1 3 through valve 80, line 81, failsafe device 12 and line 19. A continuous flow of oxygen through the nure 16 is established and oxygen is delivered to the patient via the nasal appliance 17. supplied to The flow rate of oxygen is regulated by a flow control orifice 20.

In the normal mode of operation of the volume control device 70, upon detecting the onset of patient volition, the valve is activated. 80 is moved to the other position. In this other position, valve 80 is in line 8 1 and the cannula 16 are directly connected. Next, the spring 73 moves the piston 71 to the left. push the oxygen out before it is directed through the connecting line to the patient. simultaneous Then, due to the force of the spring 24 and the air pressure in the chamber 83, the fail-safe piston is activated. The cylinder 22 is pushed to the left end of the 7 cylinder 21. The check valve 87 in line 88 is Air passes through bleed orifice 85 to refill chamber 83. De After completing the delivery of the oxygen dose contained within the placer 70, the device closes the valve 80. or return to its first position to begin a new cycle. understood However, each time valve 80 delivers a dose, fail-safe device 12 is reset. be done. The time interval between the delivery of the final gas dose and the establishment of continuous flow , the flow rate allowed by the bleed orifice 85, and the force of the spring 24. You can change it by changing it.

The fail-safe device 12 shown in FIG. It can also be successfully used as a displacer. Blowdown type metering device is a piston The ton 71 is fixed and the gas in the metering chamber is expanded at about the same time. The illustrated displacer 70 is energized to supply oxygen to the patient. It's different.

Sometimes the amount of oxygen delivered to the patient may be slightly altered based on the patient's breathing rate. and (e.g., the volume of gas delivered per dose as the breathing rate decreases) It may be desirable to increase This as well as the oxygen The fail-safe device is achieved by the method shown in Figure 6 without using electrical circuits. Ru. FIG. 6 shows the present invention which can be considered as a modification of the one explained in relation to FIG. An example of this is shown. The operation of the device shown in FIG. not due to pneumatic interaction with the safety unit 12, but due to mechanical interaction. The operation is very similar to that of the device in Figure 5, except that it is by action. Ru. In this embodiment, the failsafe unit 12 is attached to the piston 22. a piston rod 91 extending through the nolinder end 23 and extending through the nolinder end 23; It functions like a piston rod with a piston rod 91 terminating in a closed end 92. Ru. The unit 12 is arranged in alignment with the displacer 70 and is The chamber piston 71 is connected to the rod end 75 of the metering piston and the fail-safe piston. The engagement of the rod with the rod end 92 limits its movement.

When the valve 80 is in the unenergized position shown, the displacer The metering chamber 93 of 70 is filled with oxygen, and the pressure of the supplied oxygen causes the metering chamber 93 to be filled with oxygen. Stone 7j is pressed to the right. When the piston 71 approaches its end position, the spring Due to the force of 24 and the air pressure in the spring compartment 83, movement to the right is further resisted. Ru. The longer valve 80 is in its deenergized position, the more piston 22 will be pushed to the right. Therefore, the distance delivered by the next dose delivery signal increases The product 93 becomes larger. For a given dose delivery signal that biases valve 80 to the other position, If the piston 22 does not receive any time or the power is cut off, the piston 22 Gradually move to the right until port 86 is opened. By opening port 86, A continuous flow of orifice-controlled oxygen to the patient is established.

Thus, according to this embodiment, the dose volume is varied according to the patient's respiration rate and Give a continuous metered flow in the absence of a signal requiring a metered dose. It will be understood that it is possible to If such a signal occurs again and normal operation of the equipment When the operation (constant operation) resumes, the failsafe unit l-12 itself automatically shuts down. Reset for normal operation. Also, this embodiment of the invention Adjustable and fixed volume control channel that adjusts the chamber size depending on the position of I. It operates similarly to a chamber or blowdown volumetric chamber.

FIG. 7 is an alternative embodiment of the apparatus of FIG. In this example, the failsafe The unit 12 and displacer 70 are constructed similarly to the previous embodiment, and the control The movement of the volume chamber piston 7I is ensured by its piston rod end 75 and fail-safe. Limited by engagement with piston rod end 92. Control ch of displacer 70 When the chamber 93 is filled, the pressure of the oxygen supplied causes the piston 71 to move to the right. Pressed. After the piston rod end 75 and the rod end 92 are engaged, the piston 71 Further movement to the right is due to the combination of the resistance of springs 73.24 and the air pressure in spring compartment 83. Resisted by force. The longer the valve 80 is in the deenergized position shown, the more the piston The distance that the button 71 is pushed to the right increases. Force valve 80 to the other position does not receive any dose delivery signal for a given period of time or if the power supply is interrupted. In this case, the piston 71 is moved until the port 95 in the side wall of the cylinder 72 is fully opened. Eventually move. This allows from source 13 to valve 80, conduit 82, and display. A continuous flow of oxygen is established through the laser 70 and line 19, and the cannula 16 and It is delivered to the patient via the nasal appliance 17. Orifice 20 controls the flow rate. this Fail-safe device 12 prevents device 1 from resuming normal operation of the displacer. 2 reset itself. Compared to the embodiment of FIG. 6, this embodiment - The volume of gas delivered per dose changes automatically according to the It is even better in that it increases as the person's breathing rate decreases.

FIG. 8 shows yet another embodiment of the invention, in which the valve or The flow control function of fail-safe unit 12 is separated from its operating function (1 ). As in other embodiments, this unit 12 has a piston 22 disposed therein. The piston 22 is moved into the cylinder by the force of the spring 24. It is pressed toward one end of the conductor 21. The piston 22 has a piston rod 9 7 is attached, and the piston rod 97 is connected to the spring biased side of the cylinder 21. It extends through the end and terminates in connector means 99. the other end of the cylinder 21 A conduit 101 extends therethrough, which conduit 101 connects the cylinder space 103 and the external gas. It communicates with the source. The on-off valve 105 is provided with valve actuation means 107. and the valve actuation means includes a piston rod 97 actuated via connector means 99. activated by Valve 105 is always closed and inlet line 109, outlet line A port line 111 and a flow restriction orifice 113 are provided. Line 109 is A line 111 communicates with the cannula.

The failsafe device 12 shown in FIG. or the volume control device shown in Figure 4. can be configured to work. When used in combination with a flow rate one-hour supply device , the device delivers a small amount of each pulse of gas via line 101 to space 1 in cylinder 21. It is configured to be introduced into 03. The spring 24 is inserted into the space via the piston 22. The pressure acting on the gas within 103 is controlled by the cannula as described in connection with FIG. This causes a gradual gas bleed that returns to the original state. Gas pulses are supplied in a timely manner The gas in space 103 is renewed as long as Push to the right repeatedly. However, if enough time passes between gas doses, the empty The gas in the space +03 is exhausted, and the piston 22 can approach the left end of the cylinder 21. Ru. Valve actuator +07 is connected to actuator 107 via connector 99. The leftward end movement of the acting piston rod 97 causes the valve 105 to open. It is composed of As a result, the flow I set by the control orifice 113 is A flow can be established between the water source and the cannula.

When used in the volume control device shown in FIG. so that the tube 101 communicates with the interior of the volumetric chamber through the bleed orifice. It is composed of Thus, while the volumetric chamber holds the gas dose, the piston 22 is slowly pushed to the right. However, the control channel Each time a quantity is released, the space 103 is depressurized and the piston 22 returns to the left. .

For some reason, the volume control device stops cycling and the supply pressure drops. When a forceful gas dose is retained in the metering chamber, the piston 22 moves to the right. Continue to do so. In this case, the valve actuator 107 is connected to the piston 22 and the piston rod. The end movement of the pad 97 to the right acts on the actuator 107 via the connector 99. The valve 105 is opened when the valve 105 is opened. At this time, as mentioned above, A controlled flow from the gas source to the cannula is established. As an example of modification of the embodiment shown in FIG. Then, when normal operation of the delivery system resumes, valve 105 closes to provide emergency oxygen to the patient. Can be configured to stop the flow.

The design and construction of the embodiments described above may be made without departing from the scope of the invention as claimed. , various changes can be made.

Flθ, 3 Breathing gas supply 2!13 international search report

Claims (12)

[Claims] 1. Provides continuous gas flow to the patient when the pulse-dose breathing gas delivery device fails In a fail-safe device used in the pulsed dose delivery device for a movable piston disposed within the conductor, the piston being compressed by elastic pressing means; is pressed in the direction of the first end of the cylinder, and is opposite to the pressing direction of the pressing means. direction and in synchronization with the cycling of the pulsed dose delivery device. means for periodically applying a gas force to the piston end; The generated force overcomes the force of the pressing means and pushes the piston to the other end of the cylinder. of the pulsed dose delivery device. reducing the force of the pressurized gas acting on the piston end in response to cyclic operation; and the piston is moved in the direction of the first end of the cylinder by the action of the pressing means. means for returning the piston to a predetermined position within the cylinder; actuated valve means such that reaching of the piston to the predetermined position is controlled by the patient. occurring at a predetermined time after delivery of a gas dose to a person, said valve means, when actuated, A face characterized in that it is adapted to supply a continuous controlled flow of inspired gas to a patient. Lusafe device. 2. Said means for reducing the force of gas acting on said piston end comprises said pulse claim characterized in that it is activated immediately after delivery of the gas dose to the patient by the dose delivery device; The fail-safe device according to Item 1 of the Scope of Claims. 3. Said means for reducing the force of gas acting on said piston end comprises said pulse Claim characterized in that it is activated upon delivery of a gas dose to a patient by a dose delivery device. A fail-safe device according to item 1. 4. the pulsed dose gas supply device employs a two-position valve for flow-time control; the two-position valve provides a bleed flow of gas into the interior of the cylinder in a first position; and simultaneously forming a pulsed dose of gas to the patient in a second position. The filter according to claim 1, characterized in that the gas pressure within the cylinder is reduced. safety device. 5. The means for reducing the gas pressure acting on the piston bypasses a check valve. a bypass line for directing gas flow to the cylinder; It is equipped with a preed orifice that limits the flow rate, and the check valve is connected to the cylinder. Claim 4 is characterized in that the device is configured to allow only the flow of Fail-safe devices as described in Section. 6. the pulsed dose gas supply device is a volumetric displacer; The racer consists of a closed cylinder in which a piston is arranged, the piston being one arranged so that it can be moved from one cylinder end to the other. The fail-safe device according to claim 1, characterized in that: 7. The boat on the cylinder wall of the displacer and the series of the failsafe device and a conduit means communicating with the inner end of the conductor, the conduit means having a check valve. and the check valve prevents flow toward the cylinder port of the displacer. A bypass line is provided that bypasses the check valve, allowing only A bleed orifice is provided on the pass line, and the bleed orifice , allowing gas to flow slowly bypassing the check valve. A fail-safe device according to claim 6. 8. The pulsed dose gas supply device comprises a body comprising a piston operating within a cylinder. It is an accumulation control displacer, in which the piston is moved to one side of the cylinder by an elastic return means. the displacer is pressed toward one end of the control displacer and the displacer is a two-position flow control valve. , wherein the flow control valve is in its first position connected to the source of breathing gas. through conduit means to the side of said displacer opposite said elastic return means. an inner end of the cylinder and a cylinder of the fail-safe device opposite the pressing means; the flow control valve is connected to an inner end of the breathing gas valve in its second position; a source of gas is isolated from the device and the cylinder of the displacer and the cylinder of the displacer and the Connecting the cylinder of the fail-safe device to a conduit means capable of directing gas to the patient The fail-safe device according to claim 1, characterized in that: 9. The pressing means of the cylinder of said fail-safe device opens a compartment provided with ventilation means. wherein the ventilation means includes a bleed orifice and a check valve; A bleed orifice restricts the flow of gas exiting the compartment, and the check valve The claim is characterized in that the compartment is arranged so that gas can quickly flow into the compartment. The fail-safe device according to item 8 of the scope of demand. 10. The pulsed dose gas supply device is a volume controlled gas supply device with a fixed volume metered chamber. a dose displacer, the metering chamber displacing the atmosphere to provide a single dose; The chamber is filled with breathing gas at a pressure higher than the Claim 1, characterized in that the delivery of the dose to the patient is energized. Fail-safe device as described. 11. Increase the magnitude of the gas dose delivered to the patient as the patient's breathing rate decreases. the capacitance, the capacitance being The check valve is arranged in parallel with the cylinder of the safety device, and the check valve and the cylinder are connected to each other. a chamber disposed between the chamber and the bleed orifice. Claim 5, characterized in that the device is filled and emptied through the check valve. The fail-safe device according to paragraph 7 or paragraph 7. 12. Provide a controlled dose of pressurized breathing gas to the patient in synchrony with the patient's breathing cycle. If a pulsed-dose breathing gas delivery device is used to a pulsed-dose breathing gas supply that provides a continuous controlled flow of said breathing gas to the patient when In a method for fail-safe operation of a supply device, the valve means is provided with an elastic pressing means. is provided, said valve means being movable from one position to another position and adapted to supply said pressurized breathing gas. cyclically supplying said valve means with said pressurized breathing gas, said valve means being resiliently compressed by said valve means; applying a force on said valve means in a direction opposite to that of the breathing gas provided by said supply device. to a patient, and upon cycling of said pulsed dose delivery device said valve means reducing the force applied to the pulsed dose delivery device so that the pulsed dose delivery device is no longer cycling. said force actuates said valve means for continuous flow of breathing gas to the patient. a pulse characterized by opening a passageway and delivering a gas dose to the patient for a predetermined period of time; A method for providing fail-safe operation of a dose breathing gas delivery device.