|Número de publicación||US3882847 A|
|Tipo de publicación||Concesión|
|Fecha de publicación||13 May 1975|
|Fecha de presentación||11 Dic 1973|
|Fecha de prioridad||11 Dic 1973|
|Número de publicación||US 3882847 A, US 3882847A, US-A-3882847, US3882847 A, US3882847A|
|Inventores||Jacobs Harvey Barry|
|Cesionario original||Jacobs Harvey Barry|
|Exportar cita||BiBTeX, EndNote, RefMan|
|Citas de patentes (2), Citada por (44), Clasificaciones (10)|
|Enlaces externos: USPTO, Cesión de USPTO, Espacenet|
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
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  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 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.
|Patente citada||Fecha de presentación||Fecha de publicación||Solicitante||Título|
|US3400713 *||12 Oct 1966||10 Sep 1968||James E. Finan||Apparatus for intermittently dispensing oxygen or other gas suitable for breathing|
|US3795240 *||29 Mar 1972||5 Mar 1974||Hoffmann La Roche||Respiratory distress stimulator system|
|Patente citante||Fecha de presentación||Fecha de publicación||Solicitante||Título|
|US4296757 *||14 Abr 1980||27 Oct 1981||Thomas Taylor||Respiratory monitor and excessive intrathoracic or abdominal pressure indicator|
|US5203343 *||14 Jun 1991||20 Abr 1993||Board Of Regents, The University Of Texas System||Method and apparatus for controlling sleep disorder breathing|
|US5277194 *||4 Jun 1991||11 Ene 1994||Craig Hosterman||Breathing monitor and stimulator|
|US5295490 *||21 Ene 1993||22 Mar 1994||Dodakian Wayne S||Self-contained apnea monitor|
|US5458137 *||15 Abr 1993||17 Oct 1995||Respironics, Inc.||Method and apparatus for controlling sleep disorder breathing|
|US5611349 *||11 May 1995||18 Mar 1997||I Am Fine, Inc.||Respiration monitor with simplified breath detector|
|US5727562 *||11 Jul 1996||17 Mar 1998||Beck; Gregory S.||Pneumatically sensed respiration monitor & method|
|US6029660 *||12 Dic 1997||29 Feb 2000||Resmed Limited||Substance delivery apparatus|
|US6029665 *||14 Oct 1997||29 Feb 2000||Resmed Limited||Determination of patency of airway|
|US6085747 *||27 May 1997||11 Jul 2000||Respironics, Inc.||Method and apparatus for controlling sleep disorder breathing|
|US6091973 *||11 Abr 1996||18 Jul 2000||Resmed Limited||Monitoring the occurrence of apneic and hypopneic arousals|
|US6138675 *||16 Sep 1997||31 Oct 2000||Resmed Ltd.||Determination of the occurrence of an apnea|
|US6152129 *||14 Ago 1997||28 Nov 2000||Resmed Limited||Determination of leak and respiratory airflow|
|US6182657||18 Sep 1996||6 Feb 2001||Resmed Limited||Pressure control in CPAP treatment or assisted respiration|
|US6213119||17 Oct 1996||10 Abr 2001||Resmed Limited||Inspiratory duration in CPAP or assisted respiration treatment|
|US6237592||3 Jul 1996||29 May 2001||Resmed Limited||Auto-calibration of pressure transducer offset|
|US6237593||31 Mar 1998||29 May 2001||Resmed Limited||Estimation of flow and detection of breathing CPAP treatment|
|US6253764||7 May 1997||3 Jul 2001||Resmed, Ltd.||Control of delivery pressure in CPAP treatment or assisted respiration|
|US6279569||14 Mar 2000||28 Ago 2001||Resmed Limited||Determination of leak and respiratory airflow|
|US6332463||13 Sep 1996||25 Dic 2001||Resmed Limited||Flow estimation and compensation of flow-induced pressure swings in CPAP treatment and assisted respiration|
|US6363270||16 Dic 1999||26 Mar 2002||Resmed Limited||Monitoring the occurrence of apneic and hypopneic arousals|
|US6367474||19 Ene 1998||9 Abr 2002||Resmed Limited||Administration of CPAP treatment pressure in presence of APNEA|
|US6397841||18 Jun 1998||4 Jun 2002||Resmed Limited||Apparatus for supplying breathable gas|
|US6526974||22 Ago 2000||4 Mar 2003||John William Ernest Brydon||Pressure control in CPAP treatment or assisted respiration|
|US6532957||23 Sep 1997||18 Mar 2003||Resmed Limited||Assisted ventilation to match patient respiratory need|
|US6635021||19 Sep 1997||21 Oct 2003||Resmed Limited||Method and apparatus useful in the diagnosis of obstructive sleep apnea of a patient|
|US6688307||12 Mar 2002||10 Feb 2004||Resmed Limited||Methods and apparatus for determining instantaneous elastic recoil and assistance pressure during ventilatory support|
|US6810876||3 Jul 2002||2 Nov 2004||Resmed Ltd.||Assisted ventilation to match patient respiratory need|
|US7004908||18 Ene 2002||28 Feb 2006||Resmed Limited||Method and apparatus useful in the diagnosis of obstructive sleep apnea of a patient|
|US7137389||15 Mar 2004||21 Nov 2006||Resmed Limited||Method and apparatus for determining instantaneous inspired volume of a subject during ventilatory assistance|
|US7141021||21 Jul 2005||28 Nov 2006||Resmed Limited||Method and apparatus useful in the diagnosis of obstructive sleep apnea of a patient|
|US7320320||15 Dic 2003||22 Ene 2008||Resmed Limited||Determination of patency of the airway|
|US7644713||8 Mar 2006||12 Ene 2010||Resmed Limited||Method and apparatus for determining instantaneous leak during ventilatory assistance|
|US7730886||28 Nov 2007||8 Jun 2010||Resmed Limited||Determination of patency of the airway|
|US8051853||19 Nov 2009||8 Nov 2011||Resmed Limited||Method and apparatus for providing ventilatory assistance|
|US8360060||28 May 2010||29 Ene 2013||Resmed Limited||Distinguishing between closed and open airway apneas and treating patients accordingly|
|US8381722||29 Sep 2010||26 Feb 2013||Resmed Limited||Distinguishing between closed and open airway apneas and treating patients accordingly|
|US8684000||22 May 2012||1 Abr 2014||Resmed Limited||Administration of CPAP treatment pressure in presence of apnea|
|US8733351||21 Sep 2011||27 May 2014||Resmed Limited||Method and apparatus for providing ventilatory assistance|
|US8752547||20 Dic 2012||17 Jun 2014||Resmed Limited||Distinguishing between closed and open airway apneas and treating patients accordingly|
|US8844537||13 Oct 2010||30 Sep 2014||Michael T. Abramson||System and method for alleviating sleep apnea|
|US20040123866 *||15 Dic 2003||1 Jul 2004||Michael Berthon-Jones||Determination of patency of the airway|
|US20050283089 *||21 Jul 2005||22 Dic 2005||Colin Sullivan||Method and apparatus useful in the diagnosis of obstructive sleep apnea of a patient|
|WO1982001815A1 *||25 Nov 1981||10 Jun 1982||Ind Inc Tritec||Respirator apparatus and method|
|Clasificación de EE.UU.||600/534, 340/573.1, 340/626|
|Clasificación internacional||A61B5/113, A61B5/11, A61M16/00|
|Clasificación cooperativa||A61B5/1135, A61M16/0051|
|Clasificación europea||A61B5/113B, A61M16/00K|