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Publication numberUS3882847 A
Publication typeGrant
Publication dateMay 13, 1975
Filing dateDec 11, 1973
Priority dateDec 11, 1973
Publication numberUS 3882847 A, US 3882847A, US-A-3882847, US3882847 A, US3882847A
InventorsJacobs Harvey Barry
Original AssigneeJacobs Harvey Barry
Export CitationBiBTeX, EndNote, RefMan
External Links: USPTO, USPTO Assignment, Espacenet
Low-Cost Pneumatic Apnea or Respiration Monitor
US 3882847 A
Abstract
Low-cost pneumatic apnea or respiration monitor adapted to sound an alarm for a patient whose breathing is controlled by a ventilator or whose respiration has ceased.
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Description  (OCR text may contain errors)

United States Patent Jacobs LOW-COST PNEUMATIC APNEA OR RESPIRATION MONITOR Harvey Barry Jacobs, 11607 Foxclove Rd., Hunters Woods, Reston, Va. 20091 Filed: Dec. 11, 1973 Appl. No.: 423,762

[76] Inventor:

U.S. Cl. 128/2 S; 128/142; 340/279 Int. Cl. A6lb 5/10; A6lm 16/00 Field of Search 128/25. DIG. 29, 203, 2 R,

References Cited UNITED STATES PATENTS 9/1968 Finan 128/203 3/1974 Franic r. 340/279 OTHER PUBLICATIONS IBM Technical Disclosure, Vol. 6, No. 6, 11/63.

[4 1 May 13,1975

Primary ExaminerRichard A. Gaudet Assistant ExaminerG. F. Dunne Attorney, Agent, or Firm-Abraham A. Saffitz [57] ABSTRACT Low-cost pneumatic apnea or respiration monitor adapted to sound an alarm for a patient whose breathing is controlled by a ventilator or whose respiration has ceased.

9 Claims, 7 Drawing Figures 1 LOW-COST PNEUMATIC APNEA OR RESPIRATION MONITOR BACKGROUND OF THE INVENTION FIELD OF THE INVENTION This invention relates to a low-cost apnea or respiration monitor which is adapted to sound an alarm for a patient whose breathing is controlled by a ventilator or which signals the stopping of breathing in a patient not on a respirator whose illness requires monitoring.

More particularly, the invention relates to a low-cost, reliable, respiration monitor which operates on simple mechanical and pneumatic principles and is not subject to electrical failure as may be caused by deterioration of electronic components such as capacitors, vacuum tubes, or transistors.

In the pneumatic system described herein, pressure from an air pressure source is modulated by chest movement to admit air to either or two air storage tanks, each of these storage tanks having an adjustable bleed valve. Each tank feeds air to a low pressure switch or valve which actuates an alarm when the pressure falls below a critical low value in the storage tanks indicating a slowing or cessation of breathing.

OBJECTS OF THE INVENTION An object of the invention is to provide a low-cost apnea or respiration monitor which is free from capacitors, vacuum tubes and other electronic components and which operates on pressure fluid principles. The pressure system is provided with time delay means to indicate by audible, visual, and other alarm means failure of breathing of the patient in either the inspriatory or expiratory phase of each respiration cycle to indicate cessation of breathing by the patient.

BRIEF DESCRIPTION OF THE DRAWING Other objects of the invention will become apparent from the following detailed description and drawings, in which:

FIG. 1 is a partially diagrammatic illustration showing the chest air valve unit connected to the appropriate pneumatic pressure sources and delay air storage tanks for inhalation and exhalation, respectively.

FIG. 2 is detail partly in section and partly in elevation of one end of the chest air valve unit showing the spring meter mechanism for the air valve piston.

FIG. 3 is a sectional view showing one of the stops at each end of the chest air valve unit which limits the reciprocating movement of air valve piston in response to inspiration and exhalation.

FIG. 4 is an elevational view of the rigid chest mounting plate which can be detached from the air valve unit when the latter is repaired or replaced.

FIG. 5 is a sectional diagrammatic view of the chest air valve unit in mid respiration.

FIG. 6 is a sectional diagrammatic view of the chest air valve unit in exhalation phase.

FIG. 7 is a sectional diagrammatic view of the chest air valve unit in inhalation phase.

The several figures herein illustrate a pressure system for an apnea monitor in which thoracic movement actuates alarms or signals. The basic principle of the pressure chest monitor system is that increments of air supplied to an air tight tank will gradually build up the pressure in that tank to the level of the source of air pressure. If the tank has a continuous slow vent or leak the maximum pressure that can be built up by a regular series of inputs will be lower because of leakage. A calibrated pressure switch or valve connected to the air tank will be actuated if the incoming increments of air continue for a time period set by the adjustable throttle valve for respiration rate. The actuation of the switch due to this change in input to the tank can be utilized to energize an alarm indicating that the input has decreased or stopped entirely. A pressure gauge connected to the tank measures the respiration rate on the lowest swing of the guages needle. The slower the respiration rate the higher the pressure is in the tank per impulse and the faster the respiration, the lower pressure per impulse. Thus, the tank acts as an adjustable timing means for varying or delaying the timing of pressure built up in the system and activating the alarm means.

FIG. I is a schematic view of an air valve 61 receiving air under pressure from source 91 through input 74 to a tubular member 66. Preferably this tube should be transparent and the impact-resistant synthetic resin known as ABS, available from the Carlon Company, has been found satisfactory. Tubular member 66 has two other ports and 76 extending respectively to air tanks 96 and 92. Each of the air tanks has an adjustable throttle valve 97 and 93 respectively, and a low pressure switch 98 and 94 respectively.

Tube 66 is supported on a breastplate 63 by means of footing members and 86, each of which holds a circular supporting unit 83 and 84. The tube 66 is snugly retained near each end by these ring-shaped members 83 and 84. Within the tube member 66 is a reciprocating unit comprising a rod 70 having an eyeshaped member 72 at one end. This member 70 is threaded to receive threaded members 68 and 69. Secured to threaded members 68 and 69 are tubular members 67 and 100. The opposite ends of the tubular members 67 and carrry-piston unitis 64 and 65. These piston units 64 and 65 are slidable within the tube 66. As shown in FIGS. 5, 6 and 7 they shift from the mid position of FIG. 6 to the left and right in accordance with the motion of rod 70.

Rod 70 may be connected at eye 72 to a snap fastener 73 that is secured to a body belt member 79 that surrounds the body of the patient. The opposite end of belt 79 as shown at the right side of FIG. 1 has a detachable hook 80 that may be secured in a corresponding opening 81 that is part of the chestplate 63.

As portrayed in FIG. 7, when the patient takes a breath, the belt 79 pulls on eye 72 drawing the rod 70 to the left. The two plungers 64 and 65 will then be positioned so the air in the pressure tank can enter tube 66 at port 74 and escape at port 76. This adds an increment of air to tank 92.

Conversely, as shown in FIG. 6, when the patient breathes out belt 70 becomes slack, allowing rod 70 to move to the left under the influence of two springs to be described presently. At this moment of exhalation, as shown in FIG. 6, the pistons 64 and 65 permit air from the pressure tank to enter at port 74 and to leave port 75 to go to tank 96.

Thus, tank 92 can be designated the inhalation tank and the tank 96 can be designated. the exhalation tank. Since both tanks are equipped with adjustable throttle valves 93 and 97, any slowness of operation of rod 70, or cessation of motion thereof, will soon result in a rise of pressure in one or the other of the two tanks. Such rise in pressure will actuate the appropriate signal alarm 95 or 99 to notify an attendant of the critical situation respecting this particular patient.

Pressure gauges H66 and 107 may be attached to timing tanks 92 and 96. To an observer, the pressure gauges will indicate the breathing conditions of the patient by registering the low and high pressure cycles in the attached tank. Too high pressure would indicate that the patients chest is not moving sufficiently for proper breathing.

The spring suspension that causes rod 76 to return to the extreme right position when not under any pull from the belt 79 is shown in detail in FIG. 2. This figure shows the left half of the rod portrayed in FlG. 1. The piston member 65 is a snug fit within the plastic tube 66 and carries a tubular member 67 which is secured to the threaded member 69 at its other end. Consequently, the weight of one end of rod 76 is carried through the agency of member 6%, tube 67 and piston 65 by the tube 66.

Exactly similar support means is found at the right end of tube 66 and rod 76 where piston 64 carries the tubular member Wt) threaded member 68 and the right end of threaded rod 70.

It will be seen that the threaded members 68 and 69 can position the pistons 64 and 65 in different lengthwise locations along rod 70 and thereby determine the interval between the passage of these pistons over the ports 75 and 76.

Referring again to FIG. 2, the tube member 67 is surrounded by coil spring 89. This coil spring is secured, as by soldering, to the tube 67 at point 101. The other end of the spring is secured, as by crimping, over the edge of tube 66. The spring 89 is under partial compression when the rod 76 is in mid position shown in FIG. 5. At this moment the other spring 88 at the right end is under partial tension. Consequently, rod '70 is released from any pull by the belt 79 will spring to the right end under the impetus of two springs. This is the situation in FIG. 6.

It is desirable that pistons 64 and 65 be limited in their extreme movements to avoid pulling them from tube 66. FIG. 3 shows such a stop member comprising a rubber grommett which fits snugly over the end of tube 66 and projects inwardly into the tube to the point where the motion of the piston is to be stopped. This grommett is indicated as 77 and 78 in FIG. 1.

FIG. 4 is a partial detail of the supporting means and the tube 66 carried by the supporting means. This figure might be regarded as the stationary portion of the air valve, the other elements moving more or less in accordance with the pull on belt '79 produced by the action of the patients chest in breathing. Footing members 85 and 86 are shown attached to the breastplate 63. The latter is shown as slightly curved at each end to conform to the human anatomy. At the top of parts 85 and 86, ring-shaped members 83 and 84 are secured and in turn carry the transparent tube 66 approximately at each end thereof. At the right end of breastplate 63 an apertured projection 81 provides means for detachably connecting the body belt "79 to the breastplate.

From the above description of a preferred embodiment of my pneumatic respiration monitor, it will be seen that no electricity is employed in the vicinity of the patient and need not be employed in the same room as the patient. lf the alarms and 99 are electrical,

they can be energized by pneumatic tubing from an adjoining room. In some situations (operating rooms, for example), electrical sparks are to be avoided at all costs. The alarms may be pneumatic, such as an air whistle.

What is claimed is:

l. A pressure fluid breathing monitor for a patient comprising:

a support,

a valve means having two relatively movable valve parts;

a body belt adapted to partly surround the patients chest;

means connecting one end of the belt to one valve part and means for connecting the other end of the belt to said support;

said valve parts moving relatively to each other in response to the inhalation and exhalation motions of the chest;

a source of pressure fluid connected to the valve means;

pressure fluid operated alarm means including two alarm devices, each connected to said valve means by a separate conduit means, one alarm responding to abnormal inhalation motion and the other to abnormal exhalation motion;

conduit means connecting said alarm means to said valve means to receive pressure fluid therefrom for operation of said alarm device;

delay means connected to said conduit means to control the time interval wherein the pressure fluid effects the activation of the alarm means; and,

said relatively movable valve parts controlling the flow from said pressure fluid source to said conduit means in response to the inhalation and exhalation motions of the chest.

2. The breathing monitor as claimed in claim 1 wherein one valve part is mounted on a support resting on the chest with one belt end connected to the support and the other belt end connected to the other valve part.

3. The breathing monitor as claimed in claim 2 wherein the movable valve parts comprise two nested outer and inner parts, with the source of pressure fluid and the conduit means connected to the other valve part.

4. The breathing monitor as claimed in claim 3 wherein the outer part comprises a tubular member secured to said support and having three spaced ports, one connected to the source of pressure fluid and the others to the conduit means, and wherein the inner part carries means to interconnect the pressure fluid source to either of said ports.

5. The breathing monitor as claimed in claim 4 wherein spring means are provided to act on the inner part to bias it to a desired position to interconnect the pressure fluid source to a port.

6. The breathing monitor as claimed in claim 4 wherein the delay means comprises a vent to permit a portion of the pressure fluid flowing to the alarm device to escape.

7. The breathing monitor as claimed in claim 6 wherein an adjustable throttle valve controls the flow through the vent.

8. The breathing monitor as claimed in claim 4 wherein the delay means comprised a fixed volume 6 tank with a throttle valve controlling the flow and the tank, an adjustable throttlevalve to control the flow quanmy of mud wlthm the tank through the vent and a conduit connecting said tank to 9. The breathing monitor as claimed in claim 5 wherein the delay means comprises a fixed volume tank connected to the conduit means, a vent connected to 5 said alarm device.

Patent Citations
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US3795240 *Mar 29, 1972Mar 5, 1974Hoffmann La RocheRespiratory distress stimulator system
Referenced by
Citing PatentFiling datePublication dateApplicantTitle
US4296757 *Apr 14, 1980Oct 27, 1981Thomas TaylorRespiratory monitor and excessive intrathoracic or abdominal pressure indicator
US5203343 *Jun 14, 1991Apr 20, 1993Board Of Regents, The University Of Texas SystemMethod and apparatus for controlling sleep disorder breathing
US5277194 *Jun 4, 1991Jan 11, 1994Craig HostermanBreathing monitor and stimulator
US5295490 *Jan 21, 1993Mar 22, 1994Dodakian Wayne SSelf-contained apnea monitor
US5458137 *Apr 15, 1993Oct 17, 1995Respironics, Inc.Method and apparatus for controlling sleep disorder breathing
US5611349 *May 11, 1995Mar 18, 1997I Am Fine, Inc.Respiration monitor with simplified breath detector
US5727562 *Jul 11, 1996Mar 17, 1998Beck; Gregory S.Pneumatically sensed respiration monitor & method
US6029660 *Dec 12, 1997Feb 29, 2000Resmed LimitedSubstance delivery apparatus
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US6363270Dec 16, 1999Mar 26, 2002Resmed LimitedMonitoring the occurrence of apneic and hypopneic arousals
US6367474Jan 19, 1998Apr 9, 2002Resmed LimitedAdministration of CPAP treatment pressure in presence of APNEA
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US7141021Jul 21, 2005Nov 28, 2006Resmed LimitedMethod and apparatus useful in the diagnosis of obstructive sleep apnea of a patient
US7320320Dec 15, 2003Jan 22, 2008Resmed LimitedDetermination of patency of the airway
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US8051853Nov 19, 2009Nov 8, 2011Resmed LimitedMethod and apparatus for providing ventilatory assistance
US8360060May 28, 2010Jan 29, 2013Resmed LimitedDistinguishing between closed and open airway apneas and treating patients accordingly
US8381722Sep 29, 2010Feb 26, 2013Resmed LimitedDistinguishing between closed and open airway apneas and treating patients accordingly
US8684000May 22, 2012Apr 1, 2014Resmed LimitedAdministration of CPAP treatment pressure in presence of apnea
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Classifications
U.S. Classification600/534, 340/573.1, 340/626
International ClassificationA61B5/113, A61B5/11, A61M16/00
Cooperative ClassificationA61B5/1135, A61M16/0051
European ClassificationA61B5/113B, A61M16/00K