WO1985005277A1 - Conduites d'ecoulement plissees d'un systeme respiratoire et accessoires - Google Patents

Conduites d'ecoulement plissees d'un systeme respiratoire et accessoires Download PDF

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Publication number
WO1985005277A1
WO1985005277A1 PCT/US1984/001323 US8401323W WO8505277A1 WO 1985005277 A1 WO1985005277 A1 WO 1985005277A1 US 8401323 W US8401323 W US 8401323W WO 8505277 A1 WO8505277 A1 WO 8505277A1
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WO
WIPO (PCT)
Prior art keywords
manifold
sides
corrugations
fitting
invention defined
Prior art date
Application number
PCT/US1984/001323
Other languages
English (en)
Inventor
Burrell E. Clawson
James Weigl
Original Assignee
Clawson Burrell E
James Weigl
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Clawson Burrell E, James Weigl filed Critical Clawson Burrell E
Publication of WO1985005277A1 publication Critical patent/WO1985005277A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/08—Bellows; Connecting tubes ; Water traps; Patient circuits
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/08—Bellows; Connecting tubes ; Water traps; Patient circuits
    • A61M16/0816—Joints or connectors
    • A61M16/0833—T- or Y-type connectors, e.g. Y-piece
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M16/00—Devices for influencing the respiratory system of patients by gas treatment, e.g. mouth-to-mouth respiration; Tracheal tubes
    • A61M16/08—Bellows; Connecting tubes ; Water traps; Patient circuits
    • A61M16/0875—Connecting tubes

Definitions

  • This invention relates to improvemen s in the circuit elements of respiratory systems and it relates in particular to corrugated flow lines and coupling members in systems whose purpose is to furnish respiratory gas to patients .
  • a generalized model of a respirator system in ⁇ cludes a source of humidified, pressurized, respiratory gas connected by a gas delivery conduit, to a system ele ⁇ ment which supplies inspiratory gas ' to the patient, and which receives expiratory gas from the patient .
  • the general model includes a conduit by which ' the expired gas is drawn • to a suction point.
  • the source and the. return point form part of o a respirator or ventila ⁇ tor which serves to control composition of the gas, supply and return pressure, gas temperature, humidity, and the frequency of supply pressure variations.
  • - ment by which gas is delivered to the patient may be a tent or an incubator or a mask or a flow manifold and nasal or endotracheal tube.
  • the respirator is portable and is pos it io ne d . ne xt to the subject's bed or incubator such as to permit connection to sources of electrical power, water, oxygen and the like.
  • the respirator is brought to the patient and his/her delivery structure is connected to the machine by flexible supply and exhaust tubing .
  • each interconnection is unique.
  • the distance and angle from the respirator to the patient are unique for each instance.
  • the ' practi ⁇ tioner selects and in erconnects pieces from the kit or assem-bly to create the breathing circuit. What remains is disposed of- as unused excess. The amount of the excess is often very, significant because the. asse ' blies and sets are arranged to accommodate a variety of types of equipment and treatments and sizes of patients.
  • the tubing constitutes a major part of most sets. To permit bending without kinking it is almost in ⁇ variably corrugated along its length except at the ends and it is formed of a resilient material,. That introduces two problems.
  • the tube cannot be "cut to fit".
  • the kit includes tubes of different lengths to insure that one will be sufficiently long. Not only is the practice wasteful of tubing material, it is wasteful of storage space at manufacture and at the facility at which it is to be used. It is wasteful, too, of shipping facilities because the bulk far exceeds the weight of the tubing, and the cost of shipping (which is computed on bulk) can be an important part of the eventual cost to .the patient who must pay for the kit.
  • the prior art corrugated tubing gives rise to additional problems.
  • Another object is to provide elements for re ⁇ spiratory gas flow circuitry which can be use to create circuits which employ fewer parts and fewer interconnec ⁇ tions and potential leak points while permitting reduced flow resistance and reduced circuit compliance , more efficient .control of condensate, and more easily managed and less unco f-or table connection, to the patient than usually is possible with corresponding prior art elements.
  • Another object is to provide such an element which can swivel and rotate through complete revolutions relative to another adjacent: element without a resilient bias and without loss of sealing against leaks.
  • a further object of the invention is to provide flow circuit elements which require only a fraction of the storage and shipping space required by conventional cir ⁇ cuit elements.
  • One of the specific objects of the invention is related to the fact that the muscular activity that results is breathing is triggered by carbon dioxide levels in the lungs. Frequently when a patient is ventilated, the carbon dioxide level falls to a level so low that the patient does not breath of his own. accord. The level can be raised without disturbing system pressure buy lengthen ⁇ ing the connection from the patient to the coupler in the supply and return circuit.
  • the invention provides a novel means for adjusting that length and, in the preferred form, for increasing volume in that connection with a minimum change in length.
  • corru ⁇ gation design for the walls of tubes a d connectors in which one side of individual corrugations ' are more wide than the other whereby in combination with the other -the wider side has the characteristics of a Bellville washer.
  • the corrugation design is such that the two sides of the corrugation are stable or relaxed in either of two, and in the preferred form, any of three states or relative posi ⁇ tions.
  • the two sides of each corrugation are joined at their common outer periphery by a hinged connection. In one relaxed condition the two sides lie nearly parallel over their whole circumference. In a second relaxed con ⁇ dition the two sides diverge from their ⁇ hinged connection over the whole of their circumferences.
  • the respiratory circuit element may be compressed to stable, shorter length or elongated to stable, longer length or bent to a stable curve of selected simple or compound radius.
  • a major advantage of the invention is that it can employ thin and relatively rigid plastic material. Elements like water trap ⁇ onnections and patient couplers or manifolds can be " molded integrally with input and, out ⁇ put tubes and patient connection tubes. These combination elements can be formed in blow molds, for example, with flow ports closed to be trimmed open as needed when the therapist constructs the breathing circuit.
  • Figure 1 is a diagramatic showing of a representative respiratory system and patient in an intensive care unit
  • Figure 2 is a length of respiratory tubing according to the invention, part of the special cor ⁇ rugations being and others compressed;
  • Figure 3 is an enlarged cross-sec io al view of the tube of Figure 2 taken at the junction of •its extended and compressed portions;
  • Figure ' 4 is a cross—sectional view of one preferred form of respiratory gas system in which the invention is embodied; " " " ,
  • Figure 5 is a view in side elevation of another preferred respiratory system circuit in which the invention is embodied
  • Figure 6 is a cross-sec ional view of the manifold taken on line 6—6 of Figure 5.
  • Figure 7 is a view in top elevation of a fragment of a unitary assembly made possible by an incorporation of the invention.
  • Figure 8 is a cross-sectional view taken on line 8-8 of Figure 7- • ' Figure 9 is an isometric view of the upper container portion of a water trap;
  • Figure 10 is a cross-sectional view showing how the water trap may be assembled of the assembly of Figure 7 ' ;
  • Figure- 11 is a top plan view, reduced in size, of the assembly of Figure 7 illustrating how it can be used;
  • Figure 12 is an enlarged cross-sectional and fragmented view taken on line 12-12 of Figure .11;
  • Figure 13 is a further enlargement of a portion of Figure 12 to illustrate mo e clear.ly how the sealing annulus is employed.
  • Figure 1 illustrates one of the many -physical arrangements by which a patient 8 can be connected to a respiratory gas supply system. . The showing is largely schematic.
  • the apparatus 10 is the respirator. It is often* called a ventilator and i s function is to provide an adequate flow of pressurized and humidified respiratory gas, usually a mixture of air and oxygen; to a patient manifold and to receive excess gas and exhaled gas from the manifold. "
  • the supply conduit is numbered 12 and the -return conduit is numbered 14. They connect to the patient manifold 16--,
  • the manifold includes a chamber through which the supply gas flows.
  • the patient's trachea "and lungs are "connected” or -"attached" to the chamber by an 'ap lication- apparatus of some kind and a flow connector.
  • the application apparatus may be a mask or tracheotomy or an endotracheal or nasal tube. In this case it is an endotracheal tube 18 and it is connected to the manifold 16 by a flow connector 20.
  • Both supply and return lines include a water trap one (22) of which is visible.
  • the manifold, connector, and tube are shown enlarged in Figure 5.
  • the endotracheal tube 18 is standard and does not form part of the invention but its inclusion illustrates the importance of the special mani ⁇ fold and connector combination.
  • the respiratory" gas usually is furnished in heated condition and at or near one hundred percent humidity. If there is any cooling, water will be condensed out of the gas. To prevent the condensate from reaching the patient the system will in- elude water traps.
  • a common practice is to drape the sup ⁇ ply and return conduits a.nd to include a trap in the sagging portion of the line. Whatever the arrangement for trapping the condensate, it will serve to limit the amount of movement permitted to the manifold and it will limit variation in manifold orientation.
  • the corrugations of the conneczor 20 are special in that they provide greater lateral flexibility than a smooth tube of the same di ⁇ ameter and much greater lateral flexibility than a conven ⁇ tional corrugated tube. Perhaps even more important, the special corrugations permit the connector to become longer and shorter as the manifold 16 and tube 18 are moved
  • the connec ⁇ tor 20 can be shortened by collapse of its corrugations and it can be extended by extension of its corrugations.
  • the connector can be bent on a small radius by collapsing individual corrugations on one side and ex ⁇ tending them on the other side of the connector, without renitency.
  • the individual- corruga ⁇ tions can assume any of ,three relaxed, stable conditions and the ma ' terial of which they are formed has sufficient stiffness and renitency to urge the corrugation into one of those relaxed conditions and to respond to external force to change from one to another of the relaxed states with -a_ snap action.
  • inner and outer circular hinges must, be relatively stiff.
  • the hinges themselves need to 'be quite flexible.
  • the walls must have 'enough resilience to bend and warp because snap , action utilizes over center spring action.
  • the art "of corrugation molding is sufficien ly advanced so that given a predictable plastic such, for example, as polypro ⁇ pylene an effective combination of material and wall thickness is readily found.
  • the manifold 16 has a lower face 24 and an upper face 26 and a cylindrical side wall 28.
  • the supply gas is introduced at an inlet port 30 and exhaust flows out of the manifold at an " outlet port 32.
  • the inlet and outlet ports are located on the upper face 26 of the manifold although either or both could have been located on the side wall 28.
  • Cylindrical fittings 34 and 36 afford communica ion with ports 30 and 32, respec ⁇ tively, and the cavity 38 of the manifold. Two more fittings, one 40 for a pressure sensor and one 42 for a temperature sensor, are visible in Figure ' 5.
  • the several corrugations of connector 20 include at least one in each of the- three relaxed states. How ⁇ ever, that is true too of the length of tubing 44 shown in Figures 2 and 3.
  • tube 44 has a cylindrical ⁇ fitting 46 at its left end. Adjacent to that fitting is a section 48 which is corrugated in conventional fashion. The remainder of the tube, to the cylind.rical fitting 50- at the right end, is formed with its wall specially corru ⁇ gated.
  • the several corrugations of the group 52, in ⁇ cluding corrugations 54-and 56 have the first relaxed state in which the two sides of the corrugation lie ' somevhat parallel.
  • the next two corrugations, 58 and 60 have the second r elax ed .
  • any of the special corrugations can have any one of the three relaxed states if the tube is made of stiff material that is sufficiently rigid to resist .chan e from one state to another unless subjected to external force.
  • cor- rugation 54 has sides 68 and 70 which are joined at circu ⁇ lar hinge 72.
  • the two sides 68 and 70 lie somewhat parallel to one another in first relaxed state.
  • the two sides 68 and 70 have a common outer diameter and equal in ⁇ ner diameters.
  • Side 68 is wider from its inner to its outer diameter than side- 70 is wide.
  • side 70 is narrower than side 68.
  • the ' .forming tool has the negative 'of the inner shape of the finished tube when all convolutions are in the second relaxed state.
  • the forming process is the same as it is for conventional cor ⁇ rugated tubing.
  • the preferred tubing material is a poly ⁇ propylene plastic. That material is relatively very stiff compared to prior art breathing tubes..
  • the amount of force required to make it change fro.m one state to another is a function of stiffness, inside and outside diameter of the corrugations and widths of the corrugation sides.
  • a representative, specially corrugated tube has an inside diameter of 0.48 inches, outside diameter of 0.68 inches, a slope relative to the tube- axis of thirty degrees at the wide side and at the narrower side a slope of negative 80 d-egrees. It is formed of polyethylene 0.005 inches thick and has a tensile strength of 4900 psi at 2"/minute and secant flexural ' modulus of 160,000 psi at .05"/minute.
  • the individual convolutions are about three times as wide in their state two o condition as they are in state one. Neglecting the end connectors, tube length can be increased and decreased by a factor of three.
  • the saving in shipping and storage volume is as important in some cases as is the flexibility and versatility the in ⁇ vention adds to the patient connection element. Also important is the facility for optimizing the arrangement of the supply and return lines between the respirator and the patient manifold. The need for a number of tubes of different length is minimized. Circuit runs may be more direct and are more readily arranged to collect condensate at a convenient and accessible point.
  • the special corru ⁇ gations are collapsed to minimize circuit length and sys ⁇ tem compliance.
  • the patient mani ⁇ fold 98 includes means for high frequency pulsing of mani ⁇ fold pressure while maintaining pressure during exhalation phase at or very near atmospheric pressure.
  • the nozzle 100 and the exhalation valve 102 are part of that means. Respiratory gas enters at the nozzle and exhaust gas is drawn off through the ex-halation valve to an outer, encompassing flowpath that ends at the cylindrical fitting 104. The latter is concentric around the nozzle 100.
  • the patient manifold 98 is connected by coaxially arranged in ⁇ ner supply conduit 108 and outer return conduit 110 " , to a respirator end water trap and manifold 112.
  • Manifold 112 includes a cylindrical return conduit fitting 114 which communicates through the manifold with a cylindrical ex ⁇ haust fi.tting 116.
  • a cylindrical supply fitting 118 is formed ' through the cavity of the manifold on the axis of fitting * 114.
  • Conduits or tubes 108 and 110 are formed with the special convolutions.. -. There is no need to match them or cut them to matching length. They can be assembled with the manifolds easily by extending the' cor ⁇ rugations of the inner conduit and compressing those of the outer conduit while connecting the ends of the inner one to nozzle 100 and fitting 118. Thereafter the inner conduit is collapsed enough to permit assembly of the outer conduit on fittings 104 and 114.
  • conduits are secure on their end fittings their length is readily adjusted over a relatively wide range by bringing the man ⁇ ifolds together or moving them apart. What, could be a difficult assembly task is made simple and easy. In use the coaxial pair exhibits much more flexible or "movea'ble" at the patient manifold than is possible to achieve with conventional soft tubes.
  • the quality that length may .,be changed does more than permit cost saving.
  • the ability to change volume in a connection provides an easy " way to change the ratio of fresh to" rebr ' eathed gas in the inspiratory ' phase. But there are other important advan ⁇ tages.
  • a particularly useful combi ⁇ nation includes the patient manifold and the supply and exhaust tubing that connects to the manifold. Another is the combination of the patient manifold and the patient connection tubing.
  • An example of the former is shown in Figure 7.
  • This assembly generally designated 130, includes a patient manifold 132 at the midregion of its length. Above the manifold , in order, are a tube section 134, a water trap manifold 136, another tube section 138 and a cylindrical end f itting 140. In order below the manifold are a tube section 142, a trap manifold 144, another tube 146 and an end fitting 148.
  • Each of the three manifolds is formed with four generally cylindrical cups extending from the outer peripher of the manifold each cup perpendicular to those on either side and all in a common plane perpendicular to the central axis of their respective manifolds. They are cups because they are molded with their outer ends closed in the preferred, method. That makes it possible to employ the inexpensive blow mold process to produce the unit. Any one of the cups is readily converted to a connector fitting .by snipping off of the closed end.
  • the four tubing sections all employ the special construction -of the invention.
  • the upper cup of the patient manifold 132 is numbered 150.
  • the lower cup, its end clipped to form a fitting is numbered 156 and is visible in Figure 12.
  • the preferred patient manifold is symmetrical about the plane parallel to the paper, in the drawing, and to the plane perpendicular to the paper which planes contain the longitudinal center line of the unit.
  • any one of the cups may have its outer end removed and serve as the fitting for attachment to the patient connection tube.
  • the preferred manner of attachment is shown in Figure 12. Consistent with the molding process, the cups are tapered to lesser diameter in the direction away from the interior of the manifold. That "draft" facilitates removal from the mold.
  • the mating connector 158 in Figure 12 has an inverse taper. In a conventional connection, the fitting that tapers to smaller diameter is fitted inside the one that is tapered or flared outwardly.
  • the flared one is the female part. It is encompassed and resiliently embraced by an elastic sealing annulus which in this case is an O-ring 164.
  • the flared fitting is the upper end of an extensible patient connection tube 166.
  • the interconnec ion between fittings 156 and 158 can be tightened by pulling the tube downwardly in Figure 12 relative to the coupler 132.
  • the relatively soft O-ring is indented by those discontinuities without lo-ss of sealing action.
  • the tube 166 is formed with a shoulder or the like at the base of fitting 158 such that -the O-ring is biased into engagement with the outer end of fitting 156 to complete the seal.
  • the preferred construc ⁇ tion is shown in Figure 13.
  • the two fittings need not. be drawn tight but the tube is left free to rotate relative to the manifold. The result is that 360 degree rotational freedom is added to the adjustable extension and bias free bending of the tube to provide structural flexibility previously unknown in respiratory circuitry.
  • the cups 150 and 154 have been left intact in Figure 12.
  • the ends of one or both, and the end of the fourth cup 162, can be cut off to accommodate pressure and temperature sensors and gas sample fittings if the thera ⁇ pist desires.
  • Manifolds 136 and 144 differ from manifold 132 in that the cups at the sides of the assembly are smaller and shaped differently than are the upper and lower cups.
  • FIG. 10 is a view in central section taken through manifold 144 and trap 174.
  • the trap is a modified version of the trap shown in our United States Patent No. x, xx, xx. It is formed by two containers 178 and 180.
  • Upper_ container 178 is press fitted into the lower , cup-shaped container 180.
  • the upper 'one is fitted with upwardly -extending straps 18-2 and 184 as. best seen in Figure 9. Diametrically placed at the sides of the -container 178, the straps are buttoned to the manifold. Strap 186 is secured by its buttonhole 186 to button 190 of container 188. Strap 192 is secured by it ' s button holes 194 and 196 to button 198 and upper cup 200, respectively, of the manifold.
  • the open end of the neck 204 has larger diameter than the diameter of the open end of fitting 202.
  • the container 178 is, or ' may be, formed of the same material as the manifold 132. Its neck may have its wall indented as it is shown to be in Figure 9 at 206 a d in that condition it is easily inserted into the fitting 202. Once inserted, the indentation is released. The neck snaps back to circular shape and connection is completed .
  • Integral formation of the supply and exhaust tu ⁇ bing with the patient manifold is important for the low cost, leak proof nature, and versatility it affords. It is pract cal because the tube portion can be made of material having the rigidity required in the manifold. Inclusion of the water trap manifolds is practical because tubing length and shape readily adjusted. The traps need to be located at or near low poi ts. That is easily arranged in the invention because the tubes are readily bent to a configuration in which the trap manifolds are low.

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  • Health & Medical Sciences (AREA)
  • Emergency Medicine (AREA)
  • Pulmonology (AREA)
  • Engineering & Computer Science (AREA)
  • Anesthesiology (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Hematology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Respiratory Apparatuses And Protective Means (AREA)

Abstract

La liaison entre un patient et un système respiratoire comprend un élément plissé de liaison (20) entre le collecteur du patient (16) et le tube endotrachéal (18) ou un autre élément d'administration. Les parois de l'élément présentent des plissements spéciaux pouvant se trouver dans l'un des trois états relaxés. Dans un état les plissements sont comprimés. Dans un deuxième état les plissements sont en extension et dans le troisième état une région des plissements présente des plissements dans le premier état et la région diamétrique des plissements présente des plissements dans le deuxième état. Des longueurs de cette conduite spécialement plissée peuvent être utilisées à la place d'une conduite conventionnelle de manière à pouvoir raccourcir et allonger selon les besoins des parties du circuit afin de réduire le nombre de différentes longueurs requises dans des installations de circuit respiratoire et d'optimiser l'agencement des conduites d'écoulement dans les circuits respiratoires.
PCT/US1984/001323 1984-05-18 1984-08-17 Conduites d'ecoulement plissees d'un systeme respiratoire et accessoires WO1985005277A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US61163284A 1984-05-18 1984-05-18
US611,632 1984-05-18

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WO1985005277A1 true WO1985005277A1 (fr) 1985-12-05

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EP (1) EP0181867A1 (fr)
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Cited By (14)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4938211A (en) * 1987-10-14 1990-07-03 Nippon Sanso Kabushiki Kaisha Breathing apparatus
GB2298470A (en) * 1995-02-28 1996-09-04 Dalatek Ltd Flexible piping
GB2306605A (en) * 1995-11-02 1997-05-07 Draftex Ind Ltd Longitudinally flexible pipe
GB2309762A (en) * 1996-02-01 1997-08-06 Sorenson Lab Inc Selectively positionable gaseous conduit orifice and method of use
US5778872A (en) * 1996-11-18 1998-07-14 Medlis, Inc. Artificial ventilation system and methods of controlling carbon dioxide rebreathing
US5823184A (en) * 1994-04-18 1998-10-20 Tyco International (Us) Inc. Breathing circuit
US6564799B2 (en) 1996-11-18 2003-05-20 Medlis Corp. Multilumen filter
US6874500B2 (en) 2001-09-24 2005-04-05 Atsuo F. Fukunaga Breathing circuits having unconventional respiratory conduits and systems and methods for optimizing utilization of fresh gases
WO2005070063A2 (fr) 2004-01-09 2005-08-04 King Systems Corporation Circuit respiratoire a longueur reglable
WO2006014167A2 (fr) * 2004-07-06 2006-02-09 Wright Vivian A Masque de nebulisation pour visage et tracheostomie
EP1621224A3 (fr) * 2001-09-24 2006-04-19 FUKUNAGA, Atsuo F. Circuit de respiration à volume et longeur réglables
US7261105B2 (en) 2001-09-24 2007-08-28 F-Concepts Llc Breathing circuits having unconventional respiratory conduits and systems and methods for optimizing utilization of fresh gases
US7717109B2 (en) 2001-09-24 2010-05-18 F-Concepts Llc Breathing systems with post-inspiratory valve fresh gas flow input, components for implementing same, and methods of use
JP2014064772A (ja) * 2012-09-26 2014-04-17 Teijin Pharma Ltd 酸素濃縮装置

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GB549361A (en) * 1941-04-16 1942-11-18 Franklin Elijah Smith Improvements in or relating to couplings for hose-pipes and other similar pipes
FR1247652A (fr) * 1959-09-23 1960-12-02 Cooper Tire & Rubber Co Tube souple
US3388705A (en) * 1965-04-08 1968-06-18 Foregger Company Inc Universal endotracheal tube coupling or adaptor
US3409224A (en) * 1967-03-13 1968-11-05 Union Carbide Corp Flexible drinking tube
US3908704A (en) * 1958-06-12 1975-09-30 Penntube Plastics Company Corrugated tubing
US3929165A (en) * 1971-12-13 1975-12-30 Ball Corp Tubular hinge assembly
US4037862A (en) * 1974-11-07 1977-07-26 Coal Industry (Patents) Limited Flexible ducting joints
US4050466A (en) * 1975-10-08 1977-09-27 Koerbacher Kathleen C Endotracheal tube
US4275724A (en) * 1979-04-02 1981-06-30 Barry Behrstock Endotracheal intubation device
US4360104A (en) * 1979-08-29 1982-11-23 Volker Lang Universal sterile closed hose system for respiration therapy apparatus
US4363323A (en) * 1980-12-04 1982-12-14 Geiss Alan C Nasogastric tube adapted to avoid pressure necrosis
US4456008A (en) * 1982-09-13 1984-06-26 Clawson Burrell E Respiratory apparatus and method

Patent Citations (12)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
GB549361A (en) * 1941-04-16 1942-11-18 Franklin Elijah Smith Improvements in or relating to couplings for hose-pipes and other similar pipes
US3908704A (en) * 1958-06-12 1975-09-30 Penntube Plastics Company Corrugated tubing
FR1247652A (fr) * 1959-09-23 1960-12-02 Cooper Tire & Rubber Co Tube souple
US3388705A (en) * 1965-04-08 1968-06-18 Foregger Company Inc Universal endotracheal tube coupling or adaptor
US3409224A (en) * 1967-03-13 1968-11-05 Union Carbide Corp Flexible drinking tube
US3929165A (en) * 1971-12-13 1975-12-30 Ball Corp Tubular hinge assembly
US4037862A (en) * 1974-11-07 1977-07-26 Coal Industry (Patents) Limited Flexible ducting joints
US4050466A (en) * 1975-10-08 1977-09-27 Koerbacher Kathleen C Endotracheal tube
US4275724A (en) * 1979-04-02 1981-06-30 Barry Behrstock Endotracheal intubation device
US4360104A (en) * 1979-08-29 1982-11-23 Volker Lang Universal sterile closed hose system for respiration therapy apparatus
US4363323A (en) * 1980-12-04 1982-12-14 Geiss Alan C Nasogastric tube adapted to avoid pressure necrosis
US4456008A (en) * 1982-09-13 1984-06-26 Clawson Burrell E Respiratory apparatus and method

Cited By (25)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4938211A (en) * 1987-10-14 1990-07-03 Nippon Sanso Kabushiki Kaisha Breathing apparatus
US5823184A (en) * 1994-04-18 1998-10-20 Tyco International (Us) Inc. Breathing circuit
GB2298470A (en) * 1995-02-28 1996-09-04 Dalatek Ltd Flexible piping
GB2298470B (en) * 1995-02-28 1998-09-09 Dalatek Ltd Flexible piping
GB2306605A (en) * 1995-11-02 1997-05-07 Draftex Ind Ltd Longitudinally flexible pipe
GB2309762A (en) * 1996-02-01 1997-08-06 Sorenson Lab Inc Selectively positionable gaseous conduit orifice and method of use
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