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Publication numberUS2490395 A
Publication typeGrant
Publication dateDec 6, 1949
Filing dateMar 17, 1947
Priority dateMar 17, 1947
Publication numberUS 2490395 A, US 2490395A, US-A-2490395, US2490395 A, US2490395A
InventorsWilm Carl C
Original AssigneeJ J Monaghan Company Inc
Export CitationBiBTeX, EndNote, RefMan
External Links: USPTO, USPTO Assignment, Espacenet
Respirator
US 2490395 A
Abstract  available in
Images(6)
Previous page
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Claims  available in
Description  (OCR text may contain errors)

C. C. WILM RESPIRATOR Dec 6, 1949 6 Sheets-Sheet 1 Filed March 17, 1947 INVENTOR. CAKL 6f IV/Ml ATTORNEY Dec. 6, 1949 c. c. WILM 2,490,395

' RESPIRATOR Filed March 17 1947 6 Sheets-Sheet 2 IN VEN TOR. CARL 6'. [VIM C C. WILM RESPIRATOH 6 Sheets-Sheet 3 Filed March 17, 1947 I N VEN TOR. 01R! 6. WI!

ATTORNEY C. C. WILM RESPIRATOR 6 Sheets-Sheet 4 Filed March 17, 1947 &

FIG. 11

INVENTOR. CARL 6'. W161 ATTORNE).

C. C. WILM RESPIRATOR Dec. 6, 1949 6 Sheets-Sheet 5 Filed March 17, 1947 INVENTOR CARL ClK M flaw ATTORNEY.

6, 1 949 c. c. WlLM 2,490,395

RESPIRATOR Filed March 17, 1947 6 sheets-sheet 6 PHA5E 3.

PHASE! PHASEZ PHAsEa I TIME IN szcowns 'JNVENTOR.

/zam ATTOQNEY.

Patented Dec. 6, 1949 RESPIRATOR Garl O. Wilm, Denver, (3010., assignor to J. J.

Monaghan Company, Inc., Denver, 0010., a corporation of Colorado Application March 1"7, 1947, Serial No. 735,162

4 Claims. 1

The present invention relates to respirators. It has to do more particularly, with respirators for patients sufiering from diseases, such as p-aralysis, of the respiratory organs. Moreover, it has to do with an improved respirator which conforms and fits the portion or portions of the patients body in such a manner as to perform its desired function, while at the same time leaving exposed other portions of the body to permit the ready access thereto for treatment purposes.

An object of the present invention is to provide an improved respirator including a bodyengaging, preferably transparent shell member having sealing means on the perimeter thereof capable of conforming to the contour and irregularities of the torso of the patient to which it is applied; it being another object to provide improved sealing means of an inflatable type including auxiliary sealing means capable of functioning when and if the inflatable sealing means becomes deflated.

Another object of the present invention is to provide an improved respirator of the foregoing character, in which a single power unit serves two separate and independent torso-engaging shell members, thus permitting the simultaneous treatment of two different patients by a single power unit.

A further object of the present invention is to provide an improved respirator including one or more torso-engaging shells having means for removably attaching them to a torso or torsos, wherein mechanism is provided for changing the atmospheric pressure within the shell or shells in accordance with the normal breathing cycle of the patient or patients being treated.

A further object of the present invention is to provide double-acting pumping means as a part of the respirator of the invention, in which the source of power for operating the pump is preferably an electric motor operated by batteries; and wherein the electric motor is provided with manually operable means permitting manual operation of the double-acting pump in the event of failure of the power means.

The foregoing and other objects and advantages of the present invention will appear from the following description and appended claims when considered in connection with the accompanying drawings forming a part of this specification wherein like reference characters designate corresponding parts in the several views.

In said drawings:

Fig. 1 is a perspective view illustrating one use of the present invention and showing a single power unit for two shells for the treatment of two different patients.

Fig. 2 is a front elevational view illustrating a full-length shell embodying the invention and shown applied to a female human.

Fig. 3 is a side elevational view of the shell and human form shown in Fig. 2.

Fig. 4 shows a half-length shell embodying the invention shown applied to a human female, the human form being shown in side elevational view with the breasts outside the area of the shell.

Fig. 5 is a front elevational view of what is shown in Fig. 4.

Fig. 6 is a front elevational view of a mid-torso shell embodying the invention shown covering substantially no more than the upper abdominal portion or region of the patient, the shell being shaped to conform to either a female or a male human.

Fig. 7 is a side elevational view of what is shown in Fig. 6.

Fig. 8 is a schematic or diagrammatic View of the respirator apparatus of the present invention disclosing a single power unit for association with two torso-engaging shell members, and illustrating generally the wiring diagram embodied in the respirator apparatus.

Fig. 9 is a top plan view of the power unit case, illustrating gauges associated therewith.

Fig. 10 is a top plan view of the power unit of Fig. 9, with the cover removed to reveal the working parts of said unit.

Fig. 11 is a side elevational view with a wall of the power unit case removed, revealing the parts within the case.

Fig. 12 is a transverse sectional view, taken through the periphery of the torso-engaging shell and sealing means of Fig. 2, illustrating the inflatable sealing means in deflated condition.

Fig. 13 is a view similar to Fig. 12, but showing the sealing means inflated.

Fig. 14 is a detail fragmentary elevational view of one form of mechanism for effecting the manual operation of the double-acting pump.

Fig. 15 is a top plan View of the valve assembly of the respirator structure of the present invention, with the valve actuating means removed.

Fig. 16 is a side elevational view, partly broken away and partly in section, of the structure shown in Fig. 15, with the valve actuating means shown in association therewith.

Fig. 17 is a right end elevational view of the structure shown in Fig. 16, looking toward the left of Fig. 16.

Fig. 18 is a diagrammatic or schematic lay-out 3 view illustrating certain optional gear assembly for the drive or power unit of the respirator; and

Fig. 19 illustrates a graph of the normal human breathing cycle created by the gear assembly of Fig. 18.

Referring now particularly to Fig. 1 of the drawings, there is shown in this figure, merely by way of illustration, one application of a respirator unit or assembly embodying the present in vention. As shown, the power unit or mechanism of the respirator is indicated as a whole at 2B and is hung, by means of brackets 2|, over the side rail 22a of a hospital cot or bed 22 upon which reposes a male patient. Spaced from the bed 22 is a similar bed or hospital cot 23 upon which reposes a female patient. The power unit or mechanism of the respirator is connected by means of a flexible conduit or tube to a preferably transparent shell 25 which is removably attached to the front portion of the torso of the male patient in bed. 22. A similar conduit or flexible tube 26 extends from the unit 20 to a generally similar and preferably transparent shell 21 which is removably positioned over the midtorso or upper abdominal portion or region of the female in bed or cot 23. Thus, it will be seen,

that one of the respirator power units supplies alternate pressure and vacuum in accordance with the normal breathing cycle of a human being, to two patients at the same time. This was impossible with previously known respirator apparatus and equipment all of which was only capable of use for one patient.

Referring now particularly to Figs. 2 to '7, inelusive, of the drawings, several forms and sizes of preferably transparent torso-engaging shells embodying the present invention, are shown. In Figs. 2 and 3, the shell. shown as a whole at 25 and corresponding to the shell applied to the male patient in Fig. 1 Of the drawings, is substantially heart shaped and of a size to fit over and cover substantially the entire front portion of a male or female torso, extending from substantially the neck region of the patient to substantially the lower part or portion of the pelvic region as shown in these figures, however, the shell 25 is applied to a female patient, it being noted that the shell covers the breasts of said patient. As best seen in the side elevational view, Fig. 3, the shell 25 has its perimeter shaped so as to conform generally to the shape of the human torso and isalso provided at its perimeter with suitable compressible and thus flexible improved sealing means, shown as a whole at 30, see also Figs. 12 and 13. Figs. 2 through '7 illustrate the shell in relationship to the female form so as to illustrate the position of the breasts relative to the shell. Since the shells will fit the female form, they must necessarily conform to the male.

The shell 25, as shown, is preferably removably attached with, however, a snug fit on the patient, by means of adjustable straps 3| and suitable buckles 32, see particularly Fig. 3.

In Figs. 4 and 5 there is shown a so-called half-length respirator shell, shown as a whole at 28, and'applied to the torso of a female patient. This shell 28 has a perimeter-engaging seal and is held in position upon the patient by a single strap 3| whose free end engages a buckle 32. The shell 28 is also shaped preferably to conform as nearly as possible to the contour or shape of the human torso and as seen in Fig. 5, has its upper portion shaped to conform generally to the outline of the female breasts, the latter being located outside the shell in this form of the invention and its mode of application. A flexible tube or conduit such as that shown at 26 in Fig. 1, is attached to the shell 28 adjacent either the right side or the left side thereof, as seen in Figs. 4 and 5.

A third type of form of respirator shell known as a mid-torso shell, is shown as a whole at 21 in Figs. 6 and '7. This shell is the same as that designated 21 in Fig. 1 of the drawings. When compared with shells 25 and 28, shell 21 will be seen as being somewhat smaller and thus designed to cover a smaller area of the patient's torso. The shell 21 is designed particularly for treatment of a patient wherein it is only necessary to provide a shell which covers little more than the upper abdominal portion or region of the patient, the breasts and breast region and the chest being left exposed as in Figs. 4 and 5 wherein shell 28 is illustrated.

The shell 21 has applied to its perimeter a sealing member 30 like the sealing members of the preceding forms and the shell is shaped so as to conform, at least generally, to the conformation, curves and shape of the human torso. As in the preceding forms, the shell 21 is removably attached with a snug-like fit to the body of the patient by means of an adjustable strap 3| and a securing buckle 32.

In each of the forms of shell, namely those indicated at 25, 28 and 21 the perimeter or marginal portion thereof has applied to it one of the sealing members 30. In Figs. 12 and 13 which, as stated above, are fragmentary sections through the shell and sealing means of Fig. 2, the parts are shown on a full scale size. The perimeter or marginal portion 25a of the shell has secured, in any suitable manner, to its under surface, the external or inflatable member 300. of the sealing means, there being provided an air intake or inflating valve 301) located in the outer or exposed portion of the inflatable tube-like member 300.. As indicated, that portion of the inflatable member which is attached to the shell portion 25a, is formed from somewhat thicker rubber or other material than the portion away from the shell rim. Located within the inflatable member 30a is a strip or pad 30c formed from porous rubber. Thus, it will be seen that the sealing means or unitv 30 comprises two thicknesses of sheet rubber to form the inflatable portion 30a thereof and the enclosed strip of porous rubber 30c.

In Fig. 1, the sealing member is shown as defiated or unin'flated, whereas in Fig. 13, it is shown as inflated. By providing the porous rubber member 300, in the event the inflatable portion 30a should accidentally leak air, the porous rubber member 300 will seal the sealing member against further leakage of air and will act as a cushion between the respirator shell and the patient's body so that the patient will not be subjected to any discomfort and no constriction or restriction of the blood vessels at any point. Moreover, the pneumatic or inflatable feature of the present improved sealing unit insures an even pressure at all points contacted by the shell or shield, the porous sponge rubber 30c preventing the possibility of any undue application of pressure at any point or points of contact. The porous rubber, as indicated, provides also a safety feature in the event the pneumatic tube portion 30a develops a leak.

It will also be appreciated that one of the im- 'portant features and advantages of the present improved type of sealing means 30 is the fact that by virtue of said sealing means, a given size of shell will adapt itself to and fit perfectly upon a great variety of sizes and shapes of human bemgs.

Referring particularly to Figs. 8 to ll, inelusive, 14 to 16, inclusive, and 19, of the drawings the mechanical units or elements which together comprise the improved respirator of the present invention, are shown.

In addition to providing dual torso-engaging shells for two different patients with each power unit, to thus double the number of patients capable of treatment by a given number of power units or respirators, one of the present features of the present invention is to produce within both shells alternate pressure and vacuum phases which actually simulate the normal breathing cycle of each of the human beings being treated, thus making the alternate application of pressure and creation of vacuum so nearly like the normal breathing of a human being as to effect the inflation and deflation of the lungs without any discomfort or exertion on the part of the patients being treated.

In Figs. 9, and 11, the power unit, so-called, of Fig. 1 of the drawings is shown in several positions. This unit 20 contains all of the actual working or moving parts of the respirator apparatus and is included in a compact arrangement within a suitable case or housing which is of such a size and weight as to permit it to be carried from place to place at will.

The artificial respirator of the present invention is particularly adapted for use in connection with patients who have been afflicted with the type of infantile paralysis which paralyzes the chest muscles, making it impossible, or at least most difiicult, for the patient to breathe of his own volition. The respirator may, however, be used in various ways, such as in cases of drowning or asphyxiation, in which it becomes necessary to produce respiration in the human being by means of some sort of mechanical contrivance or apparatus.

While the same principle involving the application of the release of negative pressure is utilized in connection with applicants respirator, it is applied to the body by means of the lightweight, pliable shell, preferably formed with plastic, and referred to above, which shell, when applied, covers no more than the chest and abdomen of the patient. By providing three types of shells, such as those disclosed in Figs. 2 to '7, inclusive, of the drawings, a shell can be chosen to fit the needs of the patients. This is important since some patients have partial use of some of their respiratory muscles. By providing the sealing means 30, referred to above, positive sealing of air is assured and this is accomplished without any undue pressure being applied to any part of the patients body. Since all of the body except the chest and abdomen are accessible at all times for physiotherapeutic treatments, the speed of recovery of the patients is considerably increased. Moreover, since the neck of the patient is completely exposed, the performing of a tracheotomy is facilitated. This particular operation often has to be performed during the acute stage of infantile paralysis in order to provide free passage for air going into or out of the lungs, since throat muscles are paralyzed and are unable to control the glottis and epiglottis, and obviously is very difficult to perform in any of the presently known types of respirators, because of the fact that the sealing elements around the neck or in the region thereof interfere greatly.

With particular reference to the shell 25 of Figs. 2 and 3, the reverse curve at the throat end or area leaves that area easily accessible for surgery.

The present respirator being, of course, of portable nature, is also very simple to install in readiness for use. In fact, it is only necessary to lay the shell on the patient, upon which breathing immediately begins, and adjust either one or two of the straps 3|, depending upon the particular shell used. This installation can be accomplished by an unskilled person in a period of time not exceeding twenty (20) seconds, whereas the application of other and known types of respirators required from 5 to 10 minutes time.

With particular reference to Fig. 8 of the drawings, current from an outside electrical source (usually volt 60 cycle alternating current) enters through an electrical conduit 40 and feeds into a rectifier unit 4| in which unit the current is changed into 6 volt, direct current, which feeds into a series of storage batteries 42. Current from these batteries flows into an electric motor 44 carrying a gear box 45. The gear box contains suitable gearing driven by the shaft of the electric motor, which gear turns or operates a crank shaft 46. This crank shaft is connected by a drive arm 4'! to a piston rod 48 of a piston or plunger 49 forming a part of a double-acting pneumatic pump 50.

The gearing in the gear box 45 is such as to drive or rotate the driven shaft 46 at the rate of 15 to 25 R. P. M., depending upon the speed of rotation of the motor as determined by setting of rheostat 60.

The operation of the two-way pneumatic pump 50 creates alternate suction and pressure which is carried through conduits or flexible tubing 5| and 52 to substantially identical valve assemblies 53 and 54, see Figs. 8, l0 and 11. A pressure gauge 55 is associated with valve assembly 53 and a similar pressure gauge 56 is associated with valve assembly 54. These gauges, as shown, are mounted in the top wall of the case 20, see particularly Figs. 9 and 11.

One of the valve assemblies is shown in detail in Figs. l5, l6, and 17 of the drawings. The assembly 53 is connected through flexible conduit or tube 5| with the left end of pump cylinder 50 and supplies alternate suction and pressure produced by the pump, the gauge 55 being connected to port 53a by a short pipe or conduit 53b to indicate the pressure and vacuum being attained. The valve assembly 53 includes adjustable valves 53c and 53d having adjustment handles 53c and 531, respectively. Figs. 15, 16, and 17 show vacuum control valve 530 and pressure control valve 53d, both constructed in an integral unit with tube 53 which is connected in series with air hose running from pump 50 to shell 25. On the vacuum stroke, valve 530 opens downward, allowing outside air to enter the system and lower the vacuum. On the pressure stroke, valve 53d opens upward, allowing air in the system to escape and lowering the pressure. Amount of vacuum or pressure desired is obtained by adjusting control knobs, which alter size of escape holes above valves, thus controlling the amount of air entering or leaving the system and therefore controlling the vacuum and pressure. Port 53a leads to gauge 55 which indicates the amount of vaculows and crankshaft arrangement.

1 um and pressure present in the system. After the air pressure and vacuum are regulated by the adjustable valves, it is conducted by flexible tubing 24 to shell 25, see Figs. 1, 2 and 8, where it produces the necessary motion of the thorax and abdomen of the male. patient who is reposing in bed 22. The amount of vacuum and pressure admitted to the shell '25 is adjusted independently by the adjustment members or knobs 53c and 53f.

which controls the speed of, rotation of the electric motor 44, or by an optional method embodied in the present invention, of utilizing a variable governor (not shown) which is incorporated in the motor assembly.

While air is being admitted to shell 25, due to the action of the piston 59, additional air is being drawn through flexible conduit or tubing 26, from shell 2'! applied to the female patient in bed 23, this air being drawn by the opposite side of piston :39 through flexible conduit 52 and its associated valve assembly 54. Should the outsidepower supply through conduit 40, Fig. 8, for

any reason fail, relay 6|, which ordinarily is maintained in an open position by flow of electricity from the outside power supply, moves into its closed position, closing the circuit from batteries 42 to flashing red light or signal 62, indicating to attendants that the power unit is now on battery operation and will continue to'function only as long as the batteries retain their electrical charge. A signal bell, buzzer, or the like may be substituted for the flashing signal light 62, if desired; or,if desired, a visible and an audible signal as well, may be used. Any or all oi these signals may be remotely connected to any part of a building or hospital, if so desired.

It is to be noted, with particular. reference to Figs. 8, l and 11 of the drawings, that the cylinder of the double-acting pump 50 is preferably mounted for horizontal swinging movement about pivot points i3, To in a substantially U-shaped bracket H carried by a standard 12 which, as shown, is mounted upon the base or floor of the rectangular case 23, see particularly Fig. 11.

This permits the cylinder 58 to be oscillated or swung from its full-line position of Fig, to the broken-line position shown in that figure, this ction being caused by the crank 4! which is connected to the outer end of connecting rod 48 and which rotates in a circle such as that indicated by the gears are preferably out so as to produce the normal breathing cycle instead of the usual sine curve which is produced by a conventional bel- The shape and cutting of the gears shown in Fig. 18 will, of course, be varied in accordance with the particular cycle which it is desirable to produce.

With reference to Fig. 19, there is shown in this figure a graph representing the breathing cycle of.a -year-old boy, merelyby way of example.

The number of breathing cycles per minute is controlled by a rheostat 60, see Figs. 8 and 9 3 The particular drive gearing illustrated'in Fig. 18 of the drawings is suitable only for use in connection with a single-acting pump. It is to be understood also that the number of cycles of breathing per minute may be conveniently controlled by means of an adjustable governor (not shown) which varies the speed of the electric motor 44. Such adjustable governor may be provided as an integral part of the motor unit.

It will be readily appreciated that it is obviously more beneficial to a patient to produce a normal type of breathing rather than an unnatural one and that by so producing this normal breathing, the recovery of the patient is considerably speeded up.

By virtue of the present structure, the respirator embodied therein may be used in an ambulance during the transporting of a patient or patients from one location to another location, it'being understood that the unit, that is the electric motor 44 and related parts for operating the pump 50, are operated from the current in the electric batteries 42. The 6-volt circuit of ambulance may be connected to unit for use over extended period of time.

may be brought into operation immediately so as to prevent any possible break in the artificial breathing to which the patient or patients are being subjected. As seen in Fig. 14, the drive arm or crank 3: mounted upon the shaft 46 and connected at its outer end to the piston rod 48 of the double-acting pump unit 50, may be caused -to rotate by means of a hand crank 15. The shaft 46 is provided with a ratchet device 46a located within the gear box 45 and also requires a circular or annular gear or rack 46b located outside the gear box and being of such a diameter as to extend outwardly beyond the wall thereof. In normal motor operation, the shaft 46 and associated parts are driven through the ratchet device 46a. When, however, the power fails, the shaft 46 may be rotated through the annular gear 46b. As shown, the crank 15 has its shank portion journaled in a suitable bearing 16, the shank portion carrying at its end a gear 11 which is adapted to-be shifted into and out of mesh with the teeth of the annular gear 4617. As seen in full lines in Fig. 14, the gears 46b and 17 are in meshed relationship, the gear Tl being shown out of mesh in its broken line position of this figure. Spring 'lfimaintains gears in out-of-mesh position during normal operation. By providing such a structure, any novice may immediately shift the hand crank 15 toward the left in Fig. 14 to cause the gears ltb and Ti to intermesh and thus permit continuation of the operation of the double-acting pump 50. Incorporation of the ratchet obviates the necessity of disconnecting any of the drive mechanism before manual operation.

Having thus described the invention, What is claimed is:

1. Means for simultaneously applying artificial respiration over areas or" the bodies of two patients, comprising: two hollow, rigid, convex shells, each of a size and shape to cover a given area on one of'said bodies; means for sealing the peripheral edges of said shells to saidbodies; an

air conduit communicating with each shell; a

pump cylinder, said air conduits communicating with opposite extremities of said pump cylinder; a piston reciprocally mounted in said cylinder between said conduits so that movement thereof in one direction will create air pressure in the first shell and a partial vacuum in the second shell, and movement in the other direction will create a partial vacuum in the first shell and air pressure in the second shell; and means for reciprocating said piston.

2. Means for simultaneously applying artificial respiration over areas of the bodies of two :patients, comprising: two hollow, rigid, convex shells, each of a size and shape to cover a given area on one of said bodies; means for sealing the peripheral edges of said shells to said bodies; an air conduit communicating with each shell; a pump cylinder, said air conduits communicating with opposite extremities of said pump cylinder; a piston reciprocally mounted in said cylinder between said conduits so that movement thereof in one direction will create air pressure in the first shell and a partial vacuum in the second shell, and movement in the other direction will create a partial vacuum in the first shell and air pressure in the second shell; means for reciprocating said piston; an enclosing case surrounding said pump cylinder and its actuating means; and suspension hooks mounted on said case for suspending the latter from the bed of one of said patients.

3. Means for simultaneously applying artificial respiration over areas of the bodies of two patients, comprising: two hollow, rigid, convex shells, each of a size and shape to cover a given area on one of said bodies; means for sealing the peripheral edges of said shells to said bodies; an air conduit communicating with each shell; a pump cylinder, said air conduits communicating with opposite extremities of said pump cylinder; a piston reciprocally mounted in said cylinder between said conduits so that movement thereof in one direction will create air pressure in the first shell and a partial vacuum in the second shell, and movement in the other direction will create a partial vacuum in the first shell and air pressure in the second shell; means for reciprocating said piston; an independent air intake check valve opening to each conduit; an independent air discharge check valve opening from each conduit; and manually operated means for independently adjusting the air flow through each valve so that the pressure and vacuum phases in each shell may be individually regulated.

4. Apparatus according to claim 1, with the addition that the pump cylinder is pivotally mounted for rocking movement during pumping operation thereof.

CARL C. WILM.

REFERENCES CITED The following references are of record in the file of this patent:

UNITED STATES PATENTS Number Name Date 2,195,744 Emerson Apr. 2, 1940 2,287,939 Kraft June 30, 1942 2,383,821 Scanlan Aug. 23, 1945 FOREIGN PATENTS Number Country Date 458,403 Great Britain Dec. 14 1936 OTHER REFERENCES Plastics, January 1946, page 29. (Copy in Div. 55 of Patent Ofiice.)

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US2287939 *Sep 21, 1939Jun 30, 1942Gen Tire & Rubber CoRespirator
US2383821 *Feb 7, 1939Aug 28, 1945 Apparatus for artificial res
GB458403A * Title not available
Referenced by
Citing PatentFiling datePublication dateApplicantTitle
US2581893 *Aug 2, 1949Jan 8, 1952J J Monaghan Company IncRespirator
US2699163 *Jun 25, 1951Jan 11, 1955Carl-Gunnar D EngstromRespirator
US2772673 *Jun 18, 1952Dec 4, 1956Conitech LtdArtificial respiration apparatus
US2863446 *Jul 8, 1953Dec 9, 1958Conitech LtdPressure regulator device for respirators
US2962022 *Dec 12, 1956Nov 29, 1960Courtin JacquesCompressed air massaging equipment
US3062215 *Sep 2, 1959Nov 6, 1962Heyns Ockert SMethod and apparatus for facilitating the processes of parturition
US3368550 *Apr 26, 1965Feb 13, 1968Harry GlascockRespiratory cuirass
US5513647 *May 3, 1994May 7, 1996Childrens Hospital IncMethod for measuring adult-type pulmonary function tests in sedated infants and apparatus therefor
US5893368 *May 15, 1996Apr 13, 1999Virginia Commonwealth UniversityMethod for lowering abdominal pressure
US5938626 *Jul 24, 1998Aug 17, 1999Virginia Commonwealth UniversityApparatus for lowering intra-abdominal pressure
US6475124 *Jul 17, 1997Nov 5, 2002Gene J. WeissAbdominal exercise device
US7108666Jan 7, 2003Sep 19, 2006Sensormedics CorporationMethod and apparatus for performing a forced expiratory maneuver in an infant
DE1099697B *Jul 16, 1957Feb 16, 1961Conitech LtdKolbenpumpe fuer ein Geraet zur kuenstlichen Beatmung
Classifications
U.S. Classification601/44
International ClassificationA61H31/02, A61H31/00
Cooperative ClassificationA61H31/02
European ClassificationA61H31/02