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Publication numberUS3566387 A
Publication typeGrant
Publication dateFeb 23, 1971
Filing dateNov 14, 1967
Priority dateNov 14, 1967
Publication numberUS 3566387 A, US 3566387A, US-A-3566387, US3566387 A, US3566387A
InventorsDavison Ellison L, Fertig Glenn H, Schoener Allen G
Original AssigneeMine Safety Appliances Co
Export CitationBiBTeX, EndNote, RefMan
External Links: USPTO, USPTO Assignment, Espacenet
Monitoring device for positive pressure breathing apparatus
US 3566387 A
Abstract  available in
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Claims  available in
Description  (OCR text may contain errors)

MONITCRING DEVICE FOR POSITIVE PRESSURE BREATHING APPARATUS Filed Nov. 14. 19e? A TTR/VEKS United States Patent O 3,566,387 MONITORING DEVICE FOR POSITIVE PRESSURE BREATHING APPARATUS Allen G. Schoener, Verona, Ellison L. Davison, Glenshaw, and Glenn H. Fertig, Cheswick, Pa., assignors to Mine Safety Appliances Company, Pittsburgh, Pa., a corporation of Pennsylvania Filed Nov. 14, 1967, Ser, No. 682,895 Int. Cl. G08b 23/00 U5. Cl. 340-279 Claims ABSTRACT OF THE DISCLOSURE The respiration pressure of a patient being treated with positive pressure breathing apparatus is used for closing an electric switch during each inhalation cycle. Every time the switch is closed an electric charge is delivered to a rst condenser, which is discharged at regular intervals, but a first electric signal indicator for excessive breathing rate will be actuated by the charge built up on the condenser if it reaches a predetermined value before the condenser is discharged. There also is a second condenser and means for charging the condenser continuously, as well as means for discharging it every time the switch is opened. A second electric signal indicator for inadequate breathing rate will be actuated by the charge built up on the second condenser if it reaches a predetermined value before that condenser is discharged.

It is among the objects of this invention to provide a device that monitors the respiratory pattern being delivered by intermittent positive pressure breathing apparatus to a patient and signals any significant deviation from that pattern. More specically, the device is designed to signal if the patient respiration pressure fails to attain a preset minimum or exceeds a preset maximum, and also to signal if the respiration rate falls below a preset minimum or exceeds a preset maximum.

The invention is illustrated in the accompanying drawing, in which the single figure is a circuit diagram for our monitoring device.

Referring to the drawing, a normally open electric switch 1 has one contact connected by a conductor 2 with one terminal of a battery 3 and the other contact connected through a resistor 4 and a conductor 5 with the other terminal of the battery. The switch may be a magnetic switch that is closed when a magnet 6 is moved close enough to it. 'The magnet may be supported by a leaf spring 7 between the switch and a movable wall, preferably in the form of a flexible diaphragm 8, that forms one wall of a housing 9. 'The side of the housing is provided with an inlet 10 that is connected by a tube 11 with the breathing hose 12 that connects any intermittent positive breathing apparatus 13 with a mask 14 worn by a patient, whereby the inside of the housing is subjected to the air or oxygen pressure in the breathing hose. During the pressure or inhalation cycle of the breathing apparatus, the gas pressure in the housing becomes great enough to cause the diaphragm to move the magnet toward the switch so that the switch will be closed. The pressure that is required for this purpose may be determined by an adjustable cam 15 that is used for pre-loading the magnet spring. Thus, the switch is closed at a preset pressure periodically at the respiration rate of the patient.

Each time the switch is actuated to a predetermined position, which is the closed position in the circuit described, a ditferentiator circuit, consisting of resistors 4 and 17 in parallel and a capacitor 18 in series with resistor 17, produces a negative pulse that causes a transistor 19 to become nonconductive for the duration of ACC the pulse. While the transistor is nonconductive, the voltage at its collector rises at a rate determined by the time constant of a variable resistor Zll and a condenser 22 which are connected by a diode 23. Those last three elements are connected in series across conductors 2 and 5. Due to the unidirectional effect of the diode, the voltage just mentioned is stored on the condenser. If the charge is allowed to build up without interruption, it will increase to the firing point of a unijunction transistor 25, whereupon a positive pulse is produced across a resistor 26 connecting this transistor with conductor 2. This causes a silicon control rectifier 27 to conduct. The rectifier connects to conductor 2 a signal indicator, such as a lamp 28, that also is connected through a resistor 29 and a normally closed reset switch 30 with conductor 5. When the lamp is lit, electric current ilows through resistor 29, thus creating a voltage drop that causes a transistor 32 to enter a nonconductive state by `way of a capacitor 33 and a resistor 34 that are connected in parallel with each other between conductor 5 and the transistor. When transistor 32 becomes nonconductive, a relay 3'5 in series with it is released, which opens the power circuit to the transistor and closes a separate circuit containing a battery 36 and an audible alarm, such as a buzzer 37. The buzzer and lamp will continue to function until a normally open reset switch 38 is closed momentarily. The two reset switches are mechanically connected so that closing switch 38 opens reset switch 30 momentarily. Switch 38 connects the relay back in circuit and reverses it to open the buzzer circuit, and opening switch 30 extinguishes the lamp and renders rectier 27 nonconductive again. It will also be seen that if there is a power failure in the main circuit, relay 35 will be released and the buzzer will sound the alarm.

The system described thus far shows that a signal or alarm is actuated whenever suicient voltage is built up on condenser 22 to tire unijunction transistor 25. However, this build-up does not occur if the respiration rate of the patient does not exceed the desired rate for which the device is set. Prevention of voltage build-up is accomplished by timing means that discharge the condenser at regular intervals short enough to normally not leave enough time for the condenser to be charged to the value necessary for firing the unijunction transistor. For example, timing means may be used that will discharge the condenser every 30 seconds, in which case variable resistor 21 is set to require more than the expected number of closings of switch 1 in 30 seconds to charge the condenser to the alarm point. Therefore, as long as the patient does not breathe faster than intended, the switch will not close enough times in 3() seconds to charge condenser 22 to the point where it will re transistor 25. However, if the respiration rate increases so that the switch is closed more frequently in the same selected period of time, a signaling voltage will be built up on the condenser.

The timer may take the form of a unijunction transistor 41 in conjunction with a capacitorl 42 and a resistor 43. The last two elements are connected across conductors 2 and 5. The three elements generate a positive pulse which is distributed across a resistor 44 at regular intervals, such as every 30 seconds, for example. When this happens a transistor 45 is made conductive momentarily and discharges condenser 22, with which it is connected in parallel. Consequently, under normal conditions the condenser is discharged every 30 seconds before it can acquire a large enough charge to cause the lamp to light and the buzzer to sound, but if the respiration rate rises above the desired value, the alarm will be actuated.

Another feature of this invention is that the device will signal in case the respiration rate of a patient falls below the minimum rate it is desired to maintain. T0 accomplish this, a condenser 50 is connected in series with a variable resistor 51 across conductors 2 and 5, so that the condenser is charged continuously at a rate controlled by variable resistor 51. If sufficient voltage is stored on this condenser, it will re a unijunction tran.- sistor 52, thereby producing a pulse across a resistor 53 which causes a silicon control rectier 54 to conduct and permit a second signal lamp 55 to light. The rectifier connects one side of the lamp `with conductor 2 and the other side is connected by a conductor 56 to a point between lamp 28 and resistor 29. When lamp 55 is lit, a current ilow is created through resistor 29 and produces a voltage drop that causes transistor 32 to enter a nonconductive state and thereby release relay 35 so that the buzzer will sound until reset switch 38 is closed again and reset switch 30 is opened simultaneously as previously explained. l

To prevent lamp 55 from lighting while the minimu respiration rate is satisfactory, which means that there are not too few respirations per minute, condenser is discharged periodically 'before suicient voltage is stored on it to tire transistor 52. This discharging of the condenser is accomplished by a transistor 60 in parallel with it. The transistor normally does not conduct, but every time the pressure switch 1 is actuated to a predetermined position, the open position as shown, a positive pulse is injected into the base of the transistor to make it conduct and discharge condenser 50. The time that it takes for a signaling voltage to build up on condenser 50 can be adjusted by variable resistor 51. A time period is selected that is slightly greater than the period between successive openings of the switch while the breathing rate is above the minimum desired, so that under normal operating conditions condenser '50 will be discharged before it can store a tiring voltage.

Due to a capacitor 61 connected between conductor 5 and the base of the transistor, and a resistor 62 connected 'between the base of the transistor and conductor 2, transistor 60 conducts only momentarily and immediately becomes nonconductive again so that charging of condenser 50 can begin again. Therefore, if the respiration pressure is not suflicient to close the switch, enough voltage will build up on condenser 50 to cause lamp 55 to light. A drop in the respiration pressure may be due to a leak in the air stream of the breathing apparatus, or to loosening or loss by the patient of the mouthpiece, face mask or tracheotomy adapter. Lighting of the lamp can mean that either the respiration rate or the respiration pressure is too low.

By the addition of further transistors to the circuits in a known manner, transistor 19 could be made nonconductive every time switch 1 is opened instead of closed, and transistor could be made conductive every time the switch is closed instead of opened.

A further feature is that this system can also be used for giving an alarm in case the respiration pressure becomes too great. This might occur if the patient suers a severe airway obstruction or a mucous block. To give such an alarm a second pressure operated switch 65 is provided that likewise may be magnetic and closed by a magnet 66 mounted on the end of a leaf spring 67 that can 4be pre-loaded by a cam 68. To move the magnet t0- ward the switch, the side of housing 9 opposite switch 1 likewise is provided with a movable wall, such as a flexible diaphragm 69, that will be moved outwardly to close switch 65 if the pressure in the housing rises above a predetermined maximum determined by the setting of cam 68. Closing of switch 65 creates a positive pulse, which is delivered to the gate of a silicon control rectifier 71 by way of a pair of resistors 72 and 73 and a capacitor 74. The pulse causes the rectifier to conduct and that connects a third signal lamp 75 into the circuit between wire 56 and conductor 2. When the lamp is lit, current `ilows through resistor 29 and creates a voltage drop to cause transistor 32 to become nonconductive. The result is that relay 35 is released and the alarm buzzer sounded. The lamp remains lit and the buzzer continues to buzz until the reset switches are operated.

To prevent a sudden but transistory increase in pressure from closing switch 65, a partition 77 is disposed inside housing 9 between inlet 10 and diaphragm 69. This partition divides the inside of the housing into two chambers that are connected by an aperture 78 in the partition. If the patient happens to cough and thereby suddenly increase the pressure in the larger chamber, this pressure will be prevented by the partition from reaching the other chamber and closing switch 65. That is, before the momentary increased pressure in the large chamber can be transmitted through the small hole in the partition to the other chamber, the breathing apparatuswill have switched to the exhalation cycle and the pressure in the housing will be reduced.

According to the provisions of the patent statutes, we have explained the principle of our invention and have illustrated and described what we now consider to represent its best embodiment. However, we desire to have it understood that, within the scope of the appended claims, the invention may be practiced otherwise than as specifically illustrated and described.

We claim:

1. A monitoring device for breating apparatus comprising an electric switch movable between open and closed positions and normally in one of said positions, means actuated by patient respiration pressure above a predetermined minimum for periodically moving the switch to the other of said positions, a rst condenser, means for charging the condenser every time the switch is actuated to said other position, means for discharging the condenser at regular intervals, a rst electric signal indicator for excessive `breathing rate adapted to be actuated in response to the charge built up on the condenser if it reaches a predetermined value before the condenser is discharged, a second condenser, means for charging the second condenser continuously, means for discharging the second condenser every time said switch returns to said normal position, and a second electric signal indicator for inadequate breathing rate adapted to be actuated in response to the charge built up on the second condenser if it reaches a predetermined value before that condenser is discharged.

2. A monitoring device according to claim 1, in which said normal position of the switch is its open position.

3. A monitoring device according to claim 1, in which said normal position of the switch is its open position, and said second condenser discharging means are effective only momentarily, whereby a charge will be built up on the second condenser to said last-mentioned predetermined value if said respiration pressure becomes insuicient to close said switch.

4. A monitoring device according to claim 1, in which said signal indicators are electric lamps, said device including an electric audible alarm, an electric circuit for energizing the alarm, a normally open switch in said circuit, and means causing that switch to close whenever either of said lamps is lit.

5. A monitoring device according to claim 1, in which each of said discharging means includes a normally nonconductive transistor in parallel with one of said condensers, and means for rendering the transistors conductive periodically.

References Cited UNITED STATES PATENTS 8/1964 Haber 128-4l9UX 8/1967 Andreasen et al. 340-239

Referenced by
Citing PatentFiling datePublication dateApplicantTitle
US3757776 *Jun 1, 1971Sep 11, 1973J BaumannVentilator for an anesthesia gas machine
US3760794 *Sep 1, 1971Sep 25, 1973Electronic Monitors IncRespiration monitoring apparatus and method
US3795240 *Mar 29, 1972Mar 5, 1974Hoffmann La RocheRespiratory distress stimulator system
US3798629 *Feb 11, 1972Mar 19, 1974Degraves JAlarm system for divers
US3824537 *May 25, 1972Jul 16, 1974Borg WarnerAnti-evasion system for vehicle unsupervised breath testers
US3848617 *Dec 29, 1972Nov 19, 1974Bendix CorpMeans for maintaining a fixed flow through a breathing regulator in an inhalation system
US3877467 *Dec 5, 1973Apr 15, 1975Plicchi GianniArtificial respiration system
US3889669 *Dec 11, 1972Jun 17, 1975Puritan Bennett CorpRespiration rate control system
US3906934 *Aug 7, 1974Sep 23, 1975Haverland William HPressure sensor-timer alarm for pressure sensitive devices
US3924611 *May 10, 1974Dec 9, 1975Galitsky Jury PetrovichSpirometer and anenometer apparatus
US3952739 *Oct 21, 1974Apr 27, 1976Airco, Inc.Fail safe system for a patient triggered respirator
US4316182 *Feb 27, 1980Feb 16, 1982Hodgson William RVentilator disconnection alarm
US4318399 *Nov 28, 1979Mar 9, 1982Aga AktiebolagRespirator apparatus
US4547768 *Dec 27, 1982Oct 15, 1985Kulhavy Karel AToilet reservoir fill alarm
US4593686 *Nov 13, 1984Jun 10, 1986Lloyd Stephen RMonitor for an anti-apnea device
US4648393 *Nov 2, 1984Mar 10, 1987Ackrad Laboratories, Inc.Breath activated medication spray
US4744356 *Mar 3, 1986May 17, 1988Greenwood Eugene CDemand oxygen supply device
US4813428 *Oct 17, 1986Mar 21, 1989Fukuda Denshi Co., Ltd.Device for detecting breathing
US5165397 *Jul 31, 1990Nov 24, 1992Arp Leon JMethod and apparatus for demand oxygen system monitoring and control
DE2227066A1 *Jun 3, 1972Dec 28, 1972 Title not available
EP0186280A2 *Oct 25, 1985Jul 2, 1986Robert LandisBreath activated medication spray
Classifications
U.S. Classification340/530, 340/608, 128/204.23, 340/606, 340/573.1
International ClassificationA61M16/00, A61B5/08
Cooperative ClassificationA61B5/0816, A61M16/0051
European ClassificationA61M16/00K, A61B5/08R