US3642005A - Endotracheal tube with inflatable cuff - Google Patents

Endotracheal tube with inflatable cuff Download PDF

Info

Publication number
US3642005A
US3642005A US10559A US3642005DA US3642005A US 3642005 A US3642005 A US 3642005A US 10559 A US10559 A US 10559A US 3642005D A US3642005D A US 3642005DA US 3642005 A US3642005 A US 3642005A
Authority
US
United States
Prior art keywords
cuff
chamber
tubule
balloon
air
Prior art date
Legal status (The legal status 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 status listed.)
Expired - Lifetime
Application number
US10559A
Inventor
Gerald E Mcginnis
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Individual
Original Assignee
Individual
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 Individual filed Critical Individual
Application granted granted Critical
Publication of US3642005A publication Critical patent/US3642005A/en
Anticipated expiration legal-status Critical
Expired - Lifetime legal-status Critical Current

Links

Images

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
    • A61M16/04—Tracheal tubes
    • A61M16/0434—Cuffs
    • A61M16/044—External cuff pressure control or supply, e.g. synchronisation with respiration

Definitions

  • the chamber is expandable as long as air is forced into the tubule and is so formed that after it has expanded to a predetermined size, at which the air pressure therein is the same as the maximum air pressure desired in the cuff, additional air forced into the chamber will expand it further without substantially changing the pressure in the cuff.
  • FIG. 1 is a side view of one endotracheal tube
  • FIG. 2 is an enlarged cross section taken on the line llIl of FIG. 1.
  • a flexible breathing tube 1 adapted to be inserted in the trachea 2, has an outer end that is exposed for connection to breathing apparatus.
  • the tube is encircled near its inner or lower end by a flexible cuff3 that is sealed to the tube.
  • the cuff normally is collapsed against the tube so that it and the tube can be inserted in the trachea. The surgeon selects a tube diameter based on his estimate of the diameter of the trachea.
  • a much smaller tube or tubule 4 is connected with the inside of the cuff and extends out along the larger tube, to which it may be attached.
  • the outer end of the tubule is formed for connection to a device that forces air into it.
  • a syringe is used for this purpose, with its nozzle or needle inserted in the outer end of the tubule.
  • an expandable chamber preferably an elastic balloon 6, is connected with the exposed portion of the tubule near its outer end.
  • the balloon encircles a length of the tubule that is provided with radial openings 7 communicating with the inside of the balloon.
  • the balloon is sealed to the tubule.
  • the balloon expands. Also, the balloon is so formed that although it requires a predetermined pressure to expand it to a given size, any additional air that is forced into it will cause it to continue to expand without any increase in air pressure. In fact, the pressure may decrease slightly as the balloon gets larger.
  • the balloon is designed so that the point at which this changeover to a substantially constant air pressure is made is one at which the air pressure in the balloon will be the same as the maximum air pressure desired in the cuff. Consequently, it will be understood that when further air is forced into the tubule after that desired maximum pressure has been reached, the balloon will continue to expand but the pressure in the system will not increase.
  • this device can be furnished with instructions to force a certain minimum volume of air into it, such, for example, as at least 4 cubic centimeters of air that can be delivered by a 50 cc. syringe.
  • the correct dimensions of the balloon for any given air pressure in the cuff can be predetermined. It is a matter of the relationship of material properties, unstretched balloon diameter and wall thickness. For example, when the rubber of which the balloon is made has a substantially constant modulus of elasticity, the maximum air pressure in millimeters of mercury required by the balloon will be one-half that modulus multiplied by the wall thickness of the balloon divided by its free or unstretched diameter, as demonstrated by the following equation for a cylindrical balloon:
  • the modulus of elasticity is not constant, a different proportion than one-half of the modulus is taken and the un stretched diameter of the balloon will be different and it will need to be stretched a different amount before maximum pressure is reached.
  • This invention contemplates both elastic and inelastic materials for the cuffs.
  • Inelastic material has advantages in the manufacture of the deviceJOn the other hand, if the cuff is elastic an inflation balloon can be chosen that will expand the cuff in a controlled manner and still accomplish the objectives of this invention. in such case the cufi should be made similarly to the balloon, by which is meant that after the cuff has been inflated to a predetermined diameter, further inflation will not result in an increase in air pressure inside the cuff.
  • the cuff can continue to expand until a seal is formed and yet the pressure of the cuff against the trachea wall will not exceed the maximum desired.
  • This invention also is applicable when the expandable chamber is not elastic throughout its area.
  • Part of the chamber may be rigid, such as a cup, with its open side closed by an elastic diaphragm or hemisphere that balloons out when air is forced into the chamber.
  • Claim 1 change "scale” to -sea1ed--.

Abstract

The inner end portion of an endotracheal tube is encircled by an inflatable cuff, to which is connected a tubule that extends toward the opposite end of the tube and is formed for connection to a source of air pressure. In communication with the tubule is an expandable chamber having an elastic wall. The chamber is expandable as long as air is forced into the tubule and is so formed that after it has expanded to a predetermined size, at which the air pressure therein is the same as the maximum air pressure desired in the cuff, additional air forced into the chamber will expand it further without substantially changing the pressure in the cuff.

Description

United States Patent McGinnis Feb. 15, 1972 [54] ENDOTRACHEAL TUBE WITH INFLATABLE CUFF [21] Appl. No.: 10,559
2,883,986 4/l959 3,407,8l7 l0/1968 De Luca et al. ..l28/349 B UX Galleher, Jr. ..128/35] Primary Examiner-Channing L. Pace AnarneyBrown, Murray, Flick & Peckham [57] ABSTRACT The inner end portion of an endotracheal tube is encircled by an inflatable cufi, to which is connected a tubule that extends toward the opposite end of the tube and is formed for connection to a source of air pressure. In communication with the tubule is an expandable chamber having an elastic wall. The chamberis expandable as long as air is forced into the tubule and is so formed that after it has expanded to a predetermined size, at which the air pressure therein is the same as the maximum air pressure desired in the cuff, additional air forced into the chamber will expand it further without substantially changing the pressure in the cuff.
8 Claims, 2 Drawing Figures ENDOTRACHEAL TUBE WITH INFLATABLE CUFF For medical patients who require a chronic intubation for periods of several days to weeks, a tracheotomy is performed and a tube is passed through the wall of the trachea and down several inches into the trachea. ln other cases the tube may be inserted by way of the mouth. in order that intermittent positive ventilation can be provided, there must be a seal around the outside of the endotracheal tube, between it and the trachea wall. Such a seal is provided by a flexible cuff which can be inflated by a syringe or the like that can increase the pressure of the air in the cuff. Correct inflation of the cuff is a difficult procedure and, in attempting to make sure of an effective seal, the cuff often is overpressurized. This results in an unnecessarily high occlusion pressure, which may cause dilation of the trachea and/or blockage of circulation, leading to necrosis at the cuff seal.
This overinflation problem is brought about by two situations. First, the person inflating the cuff has little or no feedback showing the quality of the seal obtained or the pressure at the interface. Second, a typical cuff must be elastically extended in order to provide a seal, so that even though the air pressure inside the inflated cufl" is known, the attendant has no way of knowing the pressure exerted by the cuff against the wall of the trachea. it is these two factors that have given rise to this invention. Others have attempted to solve the problem by making use of pilot or tell-tale balloons connected with the tubes through which the cuffs are inflated, but all that such balloons indicate is whether ornot there is air pressure in the cuffs. They do not tell how much pressure the cuffs are exerting against trachea walls, and they do not control that pressure.
It is an object of this invention to provide an endotracheal tube that carries an inflatable cuff which will make a good seal against the trachea wall and never exert too much pressure on it. Another object is to provide such a tube with a visible indicator of the pressure exerted by the cuff, and with means for maintaining that pressure substantially constant.
The preferred embodiment of the invention is illustrated in the accompanying drawing, in which FIG. 1 is a side view of one endotracheal tube; and
FIG. 2 is an enlarged cross section taken on the line llIl of FIG. 1.
Referring to the drawing, a flexible breathing tube 1, adapted to be inserted in the trachea 2, has an outer end that is exposed for connection to breathing apparatus. The tube is encircled near its inner or lower end by a flexible cuff3 that is sealed to the tube. The cuff normally is collapsed against the tube so that it and the tube can be inserted in the trachea. The surgeon selects a tube diameter based on his estimate of the diameter of the trachea.
In order to inflate the cuff, a much smaller tube or tubule 4 is connected with the inside of the cuff and extends out along the larger tube, to which it may be attached. The outer end of the tubule is formed for connection to a device that forces air into it. Generally, a syringe is used for this purpose, with its nozzle or needle inserted in the outer end of the tubule. After the cuff has been inflated properly, the outer end of the tubule is clamped to maintain the pressure in the cuff, unless the tubule is provided with a valve that will close when the syringe is removed.
It is a feature of this invention that there is no danger of overpressurizing the cuff and thereby causing it to exert too much pressure against the trachea wall. Accordingly, an expandable chamber, preferably an elastic balloon 6, is connected with the exposed portion of the tubule near its outer end. Most conveniently, the balloon encircles a length of the tubule that is provided with radial openings 7 communicating with the inside of the balloon. The balloon is sealed to the tubule. The use of a balloon for the purpose of indicating whether or not there is internal pressure within a cufi' is not new, but the additional function of my balloon as designed herein, i.e., control of pressure, is new and very important. its side wall must be thin and elastic enough to expand as long as air is forced into the tubule. Thus, as the cuff is inflated, the
balloon expands. Also, the balloon is so formed that although it requires a predetermined pressure to expand it to a given size, any additional air that is forced into it will cause it to continue to expand without any increase in air pressure. In fact, the pressure may decrease slightly as the balloon gets larger. The balloon is designed so that the point at which this changeover to a substantially constant air pressure is made is one at which the air pressure in the balloon will be the same as the maximum air pressure desired in the cuff. Consequently, it will be understood that when further air is forced into the tubule after that desired maximum pressure has been reached, the balloon will continue to expand but the pressure in the system will not increase.
There are two big advantages of this arrangement. In the first place, when the balloon has been expanded beyond a predetermined size the air pressure in the cuff is known and it also is known that the cuff will not exert a dangerous pressure on the wall of the trachea. in the second place, as long as the balloon is larger than the predetermined size just mentioned, it forms a reservoir of air that will maintain the pressure in the cuff substantially constant even though there may be slow leakage from it. The general practice is'to stretch the balloon to more than twice its inflated but unexpanded diameter. so the attendant can readily tell by the appearance of the balloon that there is the correct air pressure in the cuff. To make sure that the balloon is properly inflated, this device can be furnished with instructions to force a certain minimum volume of air into it, such, for example, as at least 4 cubic centimeters of air that can be delivered by a 50 cc. syringe.
The correct dimensions of the balloon for any given air pressure in the cuff can be predetermined. It is a matter of the relationship of material properties, unstretched balloon diameter and wall thickness. For example, when the rubber of which the balloon is made has a substantially constant modulus of elasticity, the maximum air pressure in millimeters of mercury required by the balloon will be one-half that modulus multiplied by the wall thickness of the balloon divided by its free or unstretched diameter, as demonstrated by the following equation for a cylindrical balloon:
d it d 0 1 dll where p is the pressure inside the balloon and cuff E is the effective modulus of elasticity of the balloon materit is the unstretched thickness of the balloon wall d is the unstretched or free diameter of the balloon d is the diameter of the stretched balloon empirically This equation is theoretical and deviations may exist, but the equation remains within practical working limits. In actual practice it may be necessary to determine the final dimensions empirically on the basis of this equation.
If the modulus of elasticity is not constant, a different proportion than one-half of the modulus is taken and the un stretched diameter of the balloon will be different and it will need to be stretched a different amount before maximum pressure is reached.
This invention contemplates both elastic and inelastic materials for the cuffs. Inelastic material has advantages in the manufacture of the deviceJOn the other hand, if the cuff is elastic an inflation balloon can be chosen that will expand the cuff in a controlled manner and still accomplish the objectives of this invention. in such case the cufi should be made similarly to the balloon, by which is meant that after the cuff has been inflated to a predetermined diameter, further inflation will not result in an increase in air pressure inside the cuff. Consequently, if the trachea is larger than expected so that the cuff does not seal against it after receiving maximum air pressure, the cuff can continue to expand until a seal is formed and yet the pressure of the cuff against the trachea wall will not exceed the maximum desired.
This invention also is applicable when the expandable chamber is not elastic throughout its area. Part of the chamber may be rigid, such as a cup, with its open side closed by an elastic diaphragm or hemisphere that balloons out when air is forced into the chamber.
lclaim:
l. The combination with an endotracheal tube having distal and proximal ends, of a normally collapsed flexible tubular cuff encircling the tube near its distal end and having opposite ends sealed thereto, a tubule extending from the cuff outwardly along said tube and having a distal end communicating with the inside of the cuff between the scale ends, the proximal end of the tubule having an inlet for air under pressure for inflating the cuff, and an expandable chamber having an elastic wall, the chamber being in communication with the tubule and being expandable by air forced into the chamber, said elastic wall being formed of material that will continue to stretch without a further increase in air pressure in the chamber as air continues to be forced into the chamber after reaching a predetermined pressure, said wall having an effective modulus of elasticity and unstretched thickness that will limit said predetermined air pressure to the pressure desired in the cuff.
2 The combination with an endotracheal tube having distal and proximal ends, of a normally collapsed flexible tubular cuff encircling the tube near its distal end and having opposite ends sealed thereto, a tubule extending from the cuff outwardly along said tube and having a distal end communicating with the inside of the cuff between the sealed ends, the proximal end of the tubule having an inlet for air under pressure for inflating the cuff, and an expandable chamber having an elastic wall, the chamber being in communication with the tubule and being expandable by air forced into the chamber, said elastic wall being formed of material that decreases in thickness as it is stretched by air forced into the chamber until the chamber has expanded to a size at which the air pressure therein is the same as the maximum air pressure desired in the cuff, and said wall having the property of then stretching further without increase in said maximum pressure as additional air is forced into the chamber to expand it more, whereby the desired air pressure in thecuff will be maintained as long as the chamber is larger than said size.
3. The combination recited in claim 2, in which said cuff is made of elastic material having the said property of said chamber elastic wall.
4. The combination recited in claim 2, in which said chamber is a balloon having a wall thickness and free diameter derived from the following equation as a guide:
where p is the pressure inside the balloon and cuff E is the effective modulus of elasticity of the balloon materi- 1,, is the unstretched thickness of the balloon wall d is the unstretched or free diameter of the balloon d is the diameter of the stretched balloon.
5. The combination recited in claim 2, in which said cuff is made of inelastic material.
6. The combination recited in claim 2, in which said chamber is a balloon.
7. The combination recited in claim 6, in which said tubule is provided with a lateral opening, and said balloon encircles the tubule and is sealed to it at opposite sides of said opening.
8. The combination recited in claim 6, in which the modulus of elasticity of the balloon material is substantially constant and the ratio of balloon wall thickness to the free diameter of the balloon multiplied by half said modulus is substantially equal to said maximum air pressure.
v UNITED STATES PATENT OFFICE CERTIFICATE OF CORRECTION Patent No. 3a haO 5 Dated February 5, 97
Inventor(s) Gerald E. McGinnis it is 'certified that error appears in the above-identified patent and that said Letters Patent are hereby corrected as shown below:
Claim 1, line 6, change "scale" to -sea1ed--.
Signed and sealed this 30th day of May 1972.
(SEAL) Attest: v
EDWARD M.FLETCHER,JR. ROBERT GO'I'TSCHALK I Abtestzing Officer Commissioner of Patents FORM PO-1050 (10-69) USCOMNPDC 60376.:69
-v u.s. GOVERNMENT PRINTING omcs I969 o-sss-au

Claims (8)

1. The combination with an endotracheal tube having distal and proximal ends, of a normally collapsed flexible tubular cuff encircling the tube near its distal end and having opposite ends sealed thereto, a tubule extending from the cuff outwardly along said tube and having a distal end communicating with the inside of the cuff between the scale ends, the proximal end of the tubule having an inlet for air under pressure for inflating the cuff, and an expandable chamber having an elastic wall, the chamber being in communication with the tubule and being expandable by air forced into the chamber, said elastic wall being formed of material that will continue to stretch without a further increase in air pressure in the chamber as air continues to be forced into the chamber after reaching a predetermined pressure, said wall having an effective modulus of elasticity and unstretched thickness that will limit said predetermined air pressure to the pressure desired in the cuff.
2. The combination with an endotracheal tube having distal and proximal ends, of a normally collapsed flexible tubular cuff encircling the tube near its distal end and having opposite ends sealed thereto, a tubule extending from the cuff outwardly along said tube and having a distal end communicating with the inside of the cuff between the sealed ends, the proximal end of the tubule having an inlet for air under pressure for inflating the cuff, and an expandable chamber having an elastic wall, the chamber being in communication with the tubule and being expandable by air forced into the chamber, said elastic wall being formed of material that decreases in thickness as it is stretched by air forced into the chamber until the chamber has expanded to a size at which the air pressure therein is the same as the maximum air pressure desired in the cuff, and said wall having the property of then stretching further without increase in said maximum pressure as additional air is forced into the chamber to expand it more, whereby the desired air pressure in the cuff will be maintained as long as the chamber is larger than said size.
3. The combination recited in claim 2, in which Said cuff is made of elastic material having the said property of said chamber elastic wall.
4. The combination recited in claim 2, in which said chamber is a balloon having a wall thickness and free diameter derived from the following equation as a guide:
5. The combination recited in claim 2, in which said cuff is made of inelastic material.
6. The combination recited in claim 2, in which said chamber is a balloon.
7. The combination recited in claim 6, in which said tubule is provided with a lateral opening, and said balloon encircles the tubule and is sealed to it at opposite sides of said opening.
8. The combination recited in claim 6, in which the modulus of elasticity of the balloon material is substantially constant and the ratio of balloon wall thickness to the free diameter of the balloon multiplied by half said modulus is substantially equal to said maximum air pressure.
US10559A 1970-02-11 1970-02-11 Endotracheal tube with inflatable cuff Expired - Lifetime US3642005A (en)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
US1055970A 1970-02-11 1970-02-11

Publications (1)

Publication Number Publication Date
US3642005A true US3642005A (en) 1972-02-15

Family

ID=21746319

Family Applications (1)

Application Number Title Priority Date Filing Date
US10559A Expired - Lifetime US3642005A (en) 1970-02-11 1970-02-11 Endotracheal tube with inflatable cuff

Country Status (1)

Country Link
US (1) US3642005A (en)

Cited By (32)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3794043A (en) * 1972-11-08 1974-02-26 Lanz Medical Prod Co Endotracheal tube with inflatable cuff and check valve
US3848605A (en) * 1973-04-23 1974-11-19 American Hospital Supply Corp Endotracheal tube with improved inflation retention means
US3858572A (en) * 1972-10-27 1975-01-07 Kendall & Co Insufflation device
US3888252A (en) * 1974-01-23 1975-06-10 Anthony J Side Powder inhaler
US4000741A (en) * 1975-11-03 1977-01-04 The Kendall Company Syringe assembly
US4033353A (en) * 1975-10-16 1977-07-05 International Paper Company Tracheostomy tube
US4185638A (en) * 1975-06-30 1980-01-29 Sandoz, Inc. Pressure indicators for inflatable cuff-type catheters
US4222377A (en) * 1977-06-27 1980-09-16 American Medical Systems, Inc. Pressure regulated artificial sphincter systems
US4266550A (en) * 1977-01-10 1981-05-12 Bruner James D Pressure indicators for inflatable cuff-type catheters
US4323072A (en) * 1980-01-18 1982-04-06 Shiley, Incorporated Cannula for a vein distention system
US4329985A (en) * 1980-01-18 1982-05-18 Shiley, Inc. Vein distention system
US4501273A (en) * 1982-09-30 1985-02-26 Mcginnis Gerald E Endotracheal tube with pressure controlled inflatable cuff
US4555242A (en) * 1984-01-19 1985-11-26 Saudagar Abdul S Urinary drainage appliance
US4633864A (en) * 1984-10-22 1987-01-06 Dacomed Corporation Speaking endotracheal tube
US4795431A (en) * 1987-01-14 1989-01-03 Walling Peter T Syringe and catheter apparatus
WO1991010465A1 (en) * 1990-01-15 1991-07-25 Vagn Niels Finsen Lomholt An air reservoir
US5235973A (en) * 1991-05-15 1993-08-17 Gary Levinson Tracheal tube cuff inflation control and monitoring system
GB2324735A (en) * 1997-04-28 1998-11-04 George Downward Cuff for a tracheal tube
US5893826A (en) * 1997-08-14 1999-04-13 Salama; Fouad A. Artificial sphincter urinary control system
US6732734B2 (en) * 2001-04-27 2004-05-11 Kuraray Co., Ltd. Pilot balloon for balloon catheters
US20070113857A1 (en) * 2005-11-23 2007-05-24 Markus Weiss Auto-inflation cuffs
US20090132043A1 (en) * 2007-11-15 2009-05-21 George Stephanie A Prosthesis with Bladder that Adjusts Girth
US20100160722A1 (en) * 2008-12-23 2010-06-24 Ams Research Corporation Penile prosthesis implantation device
US20110152762A1 (en) * 2009-12-23 2011-06-23 Hershey Adrienne A Enteral Feeding Catheter Assembly Incorporating An Indicator
US8142394B1 (en) 2010-12-23 2012-03-27 Kimberly-Clark Worldwide, Inc. Enteral feeding catheter device with an indicator
US8439862B2 (en) 2010-12-10 2013-05-14 Kimberly-Clark Worldwide, Inc. Infusion apparatus with flow indicator
DE102012112097A1 (en) 2012-12-11 2014-06-12 TRACOE medical Frankfurt Pressure-balancing device
DE102012112095A1 (en) 2012-12-11 2014-06-12 TRACOE medical Frankfurt Balancing balloon and method for its manufacture
US9078986B2 (en) 2011-11-11 2015-07-14 Ala Device, Llc Adjustable laryngeal airway (ALA) device and method of use
US9089426B2 (en) 2012-03-21 2015-07-28 Ams Research Corporation Automated implantable penile prosthesis pump system
US9937318B2 (en) * 2016-04-12 2018-04-10 Safe Medical Design, Inc. Safe urinary catheter and manufacturing method
US10092719B1 (en) 2017-09-13 2018-10-09 Airway Medix S.A. Catheter inflatable cuff pressure stabilizer

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2883986A (en) * 1957-09-24 1959-04-28 Davol Rubber Co Endotracheal cuff
US3407817A (en) * 1965-07-26 1968-10-29 Air Reduction Inc Catheter with cuff inflater and indicator
US3482576A (en) * 1966-05-09 1969-12-09 Kendall & Co Easy deflatable retention catheter
US3543759A (en) * 1969-07-14 1970-12-01 Kendall & Co Catheter with safety indicator
US3543758A (en) * 1967-08-14 1970-12-01 Kendall & Co Catheter with safety indicator

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2883986A (en) * 1957-09-24 1959-04-28 Davol Rubber Co Endotracheal cuff
US3407817A (en) * 1965-07-26 1968-10-29 Air Reduction Inc Catheter with cuff inflater and indicator
US3482576A (en) * 1966-05-09 1969-12-09 Kendall & Co Easy deflatable retention catheter
US3543758A (en) * 1967-08-14 1970-12-01 Kendall & Co Catheter with safety indicator
US3543759A (en) * 1969-07-14 1970-12-01 Kendall & Co Catheter with safety indicator

Cited By (60)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3858572A (en) * 1972-10-27 1975-01-07 Kendall & Co Insufflation device
US3794043A (en) * 1972-11-08 1974-02-26 Lanz Medical Prod Co Endotracheal tube with inflatable cuff and check valve
US3848605A (en) * 1973-04-23 1974-11-19 American Hospital Supply Corp Endotracheal tube with improved inflation retention means
US3888252A (en) * 1974-01-23 1975-06-10 Anthony J Side Powder inhaler
US4185638A (en) * 1975-06-30 1980-01-29 Sandoz, Inc. Pressure indicators for inflatable cuff-type catheters
US4033353A (en) * 1975-10-16 1977-07-05 International Paper Company Tracheostomy tube
US4000741A (en) * 1975-11-03 1977-01-04 The Kendall Company Syringe assembly
US4266550A (en) * 1977-01-10 1981-05-12 Bruner James D Pressure indicators for inflatable cuff-type catheters
US4222377A (en) * 1977-06-27 1980-09-16 American Medical Systems, Inc. Pressure regulated artificial sphincter systems
US4323072A (en) * 1980-01-18 1982-04-06 Shiley, Incorporated Cannula for a vein distention system
US4329985A (en) * 1980-01-18 1982-05-18 Shiley, Inc. Vein distention system
US4501273A (en) * 1982-09-30 1985-02-26 Mcginnis Gerald E Endotracheal tube with pressure controlled inflatable cuff
US4555242A (en) * 1984-01-19 1985-11-26 Saudagar Abdul S Urinary drainage appliance
US4633864A (en) * 1984-10-22 1987-01-06 Dacomed Corporation Speaking endotracheal tube
US4795431A (en) * 1987-01-14 1989-01-03 Walling Peter T Syringe and catheter apparatus
US4865587A (en) * 1987-01-14 1989-09-12 Walling Peter T Syringe and catheter apparatus
WO1991010465A1 (en) * 1990-01-15 1991-07-25 Vagn Niels Finsen Lomholt An air reservoir
US5255670A (en) * 1990-01-15 1993-10-26 Lomholt Vagn N F Air reservoir
US5487383A (en) * 1991-05-15 1996-01-30 Levinson; Gary Tracheal tube cuff inflation control and monitoring system
US5235973A (en) * 1991-05-15 1993-08-17 Gary Levinson Tracheal tube cuff inflation control and monitoring system
GB2324735A (en) * 1997-04-28 1998-11-04 George Downward Cuff for a tracheal tube
GB2324735B (en) * 1997-04-28 2001-06-20 George Downward A device to seal the trachea in the intubated patient
US5893826A (en) * 1997-08-14 1999-04-13 Salama; Fouad A. Artificial sphincter urinary control system
US6732734B2 (en) * 2001-04-27 2004-05-11 Kuraray Co., Ltd. Pilot balloon for balloon catheters
US7686019B2 (en) * 2005-11-23 2010-03-30 Markus Weiss Auto-inflation cuffs
US20070113857A1 (en) * 2005-11-23 2007-05-24 Markus Weiss Auto-inflation cuffs
US20090132043A1 (en) * 2007-11-15 2009-05-21 George Stephanie A Prosthesis with Bladder that Adjusts Girth
US7918782B2 (en) 2007-11-15 2011-04-05 Ams Research Corporation Prosthesis with bladder that adjusts girth
US20100160722A1 (en) * 2008-12-23 2010-06-24 Ams Research Corporation Penile prosthesis implantation device
US9402723B2 (en) 2008-12-23 2016-08-02 Ams Research, Llc Penile prosthesis implantation device
US8545391B2 (en) 2008-12-23 2013-10-01 Ams Research Corporation Penile prosthesis implantation device
US9005111B2 (en) 2008-12-23 2015-04-14 Ams Research Corporation Penile prosthesis implantation device
US8864651B2 (en) 2008-12-23 2014-10-21 Ams Research Corporation Penile prosthesis implantation device
WO2011077286A1 (en) 2009-12-23 2011-06-30 Kimberly-Clark Worldwide, Inc. Enteral feeding catheter assembly incorporating an indicator
US9132064B2 (en) 2009-12-23 2015-09-15 Avent, Inc. Enteral feeding catheter assembly incorporating an indicator
US10085922B2 (en) 2009-12-23 2018-10-02 Avent, Inc. Enteral feeding catheter assembly incorporating an indicator
US20110152762A1 (en) * 2009-12-23 2011-06-23 Hershey Adrienne A Enteral Feeding Catheter Assembly Incorporating An Indicator
EP2591764A1 (en) 2009-12-23 2013-05-15 Kimberly-Clark Worldwide, Inc. Enteral feeding catheter assembly incorporating an indicator
US9180247B2 (en) 2010-12-10 2015-11-10 Avent, Inc. Infusion apparatus with flow indicator
US8439862B2 (en) 2010-12-10 2013-05-14 Kimberly-Clark Worldwide, Inc. Infusion apparatus with flow indicator
US8672882B2 (en) 2010-12-23 2014-03-18 Kimbery-Clark Worldwide, Inc. Enteral feeding catheter device with an indicator
WO2012085711A1 (en) 2010-12-23 2012-06-28 Kimberly-Clark Worldwide, Inc. Enteral feeding catheter device with an indicator
US8142394B1 (en) 2010-12-23 2012-03-27 Kimberly-Clark Worldwide, Inc. Enteral feeding catheter device with an indicator
US9078986B2 (en) 2011-11-11 2015-07-14 Ala Device, Llc Adjustable laryngeal airway (ALA) device and method of use
US9889010B2 (en) 2012-03-21 2018-02-13 Boston Scientific Scimed, Inc. Automated implantable penile prosthesis pump system
US9522065B2 (en) 2012-03-21 2016-12-20 Boston Scientific Scimed, Inc. Automated implantable penile prosthesis pump system
US10285815B2 (en) 2012-03-21 2019-05-14 Boston Scientific Scimed, Inc. Automated implantable penile prosthesis pump system
US9089426B2 (en) 2012-03-21 2015-07-28 Ams Research Corporation Automated implantable penile prosthesis pump system
US10238824B2 (en) 2012-12-11 2019-03-26 Tracoe Medical Gmbh Pressure equalization balloon and method for the production thereof
WO2014090680A1 (en) 2012-12-11 2014-06-19 Tracoe Medical Gmbh Pressure equalising device
US9901693B2 (en) 2012-12-11 2018-02-27 Tracoe Medical Gmbh Pressure equalizing device
WO2014090679A1 (en) 2012-12-11 2014-06-19 Tracoe Medical Gmbh Pressure equalization balloon and method for the production thereof
DE102012112095A1 (en) 2012-12-11 2014-06-12 TRACOE medical Frankfurt Balancing balloon and method for its manufacture
DE102012112097A1 (en) 2012-12-11 2014-06-12 TRACOE medical Frankfurt Pressure-balancing device
US9937318B2 (en) * 2016-04-12 2018-04-10 Safe Medical Design, Inc. Safe urinary catheter and manufacturing method
US10556088B2 (en) 2016-04-12 2020-02-11 Safe Medical Design, Inc. Safe urinary catheter and manufacturing method
US10821262B2 (en) 2016-04-12 2020-11-03 Safe Medical Design, Inc. Safe urinary catheter and manufacturing method
US10821263B2 (en) 2016-04-12 2020-11-03 Safe Medical Design, Inc. Safe urinary catheter and manufacturing method
US11541203B2 (en) 2016-04-12 2023-01-03 Safe Medical Design, Inc. Safe urinary catheter and manufacturing method
US10092719B1 (en) 2017-09-13 2018-10-09 Airway Medix S.A. Catheter inflatable cuff pressure stabilizer

Similar Documents

Publication Publication Date Title
US3642005A (en) Endotracheal tube with inflatable cuff
US3794036A (en) Pressure regulated inflatable cuff for an endotracheal or tracheostomy tube
US3543751A (en) Oral airway with inflatable cuff
US4091816A (en) Double cuffed endotracheal tube
US4976261A (en) Endotracheal tube with inflatable cuffs
US2883986A (en) Endotracheal cuff
US3402717A (en) Endotracheal tube with valved balloon having a removable inflation stylet insert therein
US3734100A (en) Catheter tubes
US4089337A (en) Uterine catheter and manipulator with inflatable seal
US4019515A (en) Enemata administering device
US3850176A (en) Nasal tampon
US3211152A (en) Safety endotracheal tube cuff
US4598707A (en) Medical tube with inflation cuff
US3889688A (en) Tracheostomy tube with novel retaining means
US4324235A (en) Endotracheal tube
US3731692A (en) Tracheotomy or endotracheal tube cuff
US3863639A (en) Disposable visceral retainer
US3905361A (en) Apparatus for sealing the esophagus and providing artificial respiration and evacuating the stomach
US4367747A (en) Pneumatic dilatator for introdution into the esophagus
US4877025A (en) Tracheostomy tube valve apparatus
US3402718A (en) Endotracheal tube with valved balloon having removable inflation means and balloon rupturing means associated therewith
US4178940A (en) Pressure control systems
US4334534A (en) Emergency airway management device
US3731691A (en) Endotracheal tube and connector unit
US5462528A (en) Stomach tube