WO1999064097A1 - Double walled catheter and method of manufacture - Google Patents
Double walled catheter and method of manufacture Download PDFInfo
- Publication number
- WO1999064097A1 WO1999064097A1 PCT/GB1999/001814 GB9901814W WO9964097A1 WO 1999064097 A1 WO1999064097 A1 WO 1999064097A1 GB 9901814 W GB9901814 W GB 9901814W WO 9964097 A1 WO9964097 A1 WO 9964097A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- tube
- temperature
- helical coil
- catheter
- coil
- Prior art date
Links
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
- A61M25/00—Catheters; Hollow probes
-
- 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
- A61M25/00—Catheters; Hollow probes
- A61M25/0009—Making of catheters or other medical or surgical tubes
- A61M25/0012—Making of catheters or other medical or surgical tubes with embedded structures, e.g. coils, braids, meshes, strands or radiopaque coils
-
- 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
- A61M25/00—Catheters; Hollow probes
- A61M25/0043—Catheters; Hollow probes characterised by structural features
- A61M25/005—Catheters; Hollow probes characterised by structural features with embedded materials for reinforcement, e.g. wires, coils, braids
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F16—ENGINEERING ELEMENTS AND UNITS; GENERAL MEASURES FOR PRODUCING AND MAINTAINING EFFECTIVE FUNCTIONING OF MACHINES OR INSTALLATIONS; THERMAL INSULATION IN GENERAL
- F16L—PIPES; JOINTS OR FITTINGS FOR PIPES; SUPPORTS FOR PIPES, CABLES OR PROTECTIVE TUBING; MEANS FOR THERMAL INSULATION IN GENERAL
- F16L11/00—Hoses, i.e. flexible pipes
- F16L11/04—Hoses, i.e. flexible pipes made of rubber or flexible plastics
- F16L11/08—Hoses, i.e. flexible pipes made of rubber or flexible plastics with reinforcements embedded in the wall
- F16L11/081—Hoses, i.e. flexible pipes made of rubber or flexible plastics with reinforcements embedded in the wall comprising one or more layers of a helically wound cord or wire
-
- F—MECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
- F16—ENGINEERING ELEMENTS AND UNITS; GENERAL MEASURES FOR PRODUCING AND MAINTAINING EFFECTIVE FUNCTIONING OF MACHINES OR INSTALLATIONS; THERMAL INSULATION IN GENERAL
- F16L—PIPES; JOINTS OR FITTINGS FOR PIPES; SUPPORTS FOR PIPES, CABLES OR PROTECTIVE TUBING; MEANS FOR THERMAL INSULATION IN GENERAL
- F16L9/00—Rigid pipes
- F16L9/18—Double-walled pipes; Multi-channel pipes or pipe assemblies
-
- 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
- A61M25/00—Catheters; Hollow probes
- A61M25/0043—Catheters; Hollow probes characterised by structural features
- A61M25/0045—Catheters; Hollow probes characterised by structural features multi-layered, e.g. coated
Definitions
- This invention relates to catheters especially, but not exclusively, for intravascular sensors such as those which measure p0 2 , pC02, pH and temperature.
- Catheters are often used to introduce sensing elements into the body, particularly into a blood vessel.
- a hollow needle is used for making an initial entry into the blood vessel.
- a wire guide is then passed into the needle and the needle is then withdrawn.
- a catheter can then be slid over the wire guide and introduced into the blood vessel.
- a sensor e.g. including one or more optical fibres are then passed into the catheter.
- catheters have a small diameter and thin walls and kink easily. Should the catheter kink, the sensor may give a false reading or be damaged. Replacement of a damaged sensor is relatively expensive and while a change is made to a new sensor, monitoring of a patient's condition is interrupted.
- One object of the invention is to provide a more reliable and simpler method of producing a kink-resistant catheter. Another object is to produce a kink-resistant catheter consisting of a tube having a single wall in which a reinforcing coil is embedded and a method of its production.
- a related object is to provide a reinforced catheter suitable for introducing or guiding a sensor into human tissue, such as a blood vessel, wl ile resisting kinking and protecting the sensor from damage should the catheter be disturbed.
- Such sensors are typically constructed with sensing elements each of about 0.002 inches diameter, in the case of wire and 0.007 inches in diameter in the case of optical fibres.
- the sensor has an overall diameter of approximately 0.02 inch (0.5mm). This small size is necessary to allow the sensor to be placed in an artery through a cannula and not compromise the primary function of the cannula of monitoring blood pressure and allowing blood samples to be taken.
- the small size of the sensors means that they are fragile. Bending of optical fibre sensors results in a change in the signals. Progress has been made in reducing the impact of this by providing a second, reference wavelength but until the advent of this invention, sensor kinking remained a problem.
- a method of making a kink-resistant catheter comprising the steps of: (i) providing a helical coil, (ii) receiving the helical coil in a first tube formed from material which is flowable at a first temperature, (iii) receiving the first tube in a second tube which is heat shrinkable at a second temperature equal to or greater than said first temperature, to form an assembly, and (iv) heating the assembly to a temperature equal to or gTeater than the second temperature.
- the first tube comprises a fluorinated ethylene propylene copolymer (FEP) and the second tube comprises polytetrafluoroethylene (PTFE).
- the first tube comprises polyethylene or poiyurethane and the second tube comprises polyester, PTFE or FEP.
- FEP can be the second, heat-shrinkable tube in cases where the first tube is flowable at temperatures at which FEP does not flow but is heat-shrinkable.
- the most preferred combination is to employ a first tube which is poiyurethane and a second tube which is FEP.
- the first tube is heat flowable at a first temperature in the range 100 to 300°C (212 to 572°F) and the second tube is heat shrinkable at a second temperature equal to or greater than the first temperature and preferably in the range 150 to 350°C (302 to 662°F).
- the helical coil can be mounted on a mandrel and then introduced into the first tube, which is received within the second tube.
- a release agent may be provided on the mandrel to facilitate removal of the mandrel after formation of the reinforced catheter.
- Suitable release agents include liquid release agents such as silicone oils.
- the tubes extend beyond one or both ends of the helical coil.
- the invention also encompasses a method of making a kink-resistant catheter which method comprises forming an assembly by the steps of:-
- a cannula comprising a helical coil at least partially enveloped in a matrix, said matrix comprising a first tubular member of heat flowed material which is received in a second tubular member of heat shrunk material.
- the helical coil is metallic, for example, stainless steel and preferably the coils have a rounded cross-section, e.g. a circular cross-section.
- the first tubular member may comprise FEP, polyethylene or poiyurethane.
- the second tubular member may comprise PTFE, polyester or FEP.
- the catheter has a tapered tip, the helical coil terminating inwardly of the tip. Provision of a tapered tip greatly improves the case of introducing the catheter into a blood vessel.
- a reinforced catheter of very small wall thickness can be made by removing the second tube after the first tube has been caused to flow through turns in the helical coil.
- This can be readily achieved, for example, by providing a second tube which extends beyond an end of the first tube, forming a slit in the projecting end of the second tube after the heat shrinkage step and peeling the second tube away from the first.
- a catheter which comprises a helical coil having a plurahty of longitudinally spaced apart turns, said coil being at least partially enveloped in a matrix comprising a tubular member of heat-flowed material which extends between turns of the coil, said tubular member having an exposed outer surface and an inner surface covering said spaced apart turns.
- the reinforced catheters of the invention have the same or similar inside and outside diameters as conventional un-reinforced catheters but are extremely flexible and resistant to flattening when bent around a tight curve.
- Figure 1 is a scrap longitudinal section of a catheter of the invention
- Figure 2 is a scrap section of a spring and a mandrel which carries a release layer
- Figure 3 is a scrap section of a spring and release layer carried on the mandrel, the mandrel being received within a first tube;
- Figure 4 is a scrap section of a mandrel carrying and received within concentric first and second tubes;
- Figure 5 is a scrap section of a second embodiment of a catheter of the invention.
- a catheter 1 of the invention is shown in section in Figure 1. It is generally cylindrical and flexible and has an axial bore 2.
- Axial bore 2 is defined in the illustrated embodiment by first tubular member 3.
- Tubular member 3 is of composite structure. It comprises a matrix 4 of heat-flowed plastics material such as fluorinated ethylene propylene (FEP), polyethylene or poiyurethane.
- FEP fluorinated ethylene propylene
- a helical coil 5 is present within matrix 4 and is substantially completely encapsulated in the matrix.
- Helical coil 5 provides hoop strength to the catheter and hence kink resistance.
- Helical coil 5 is preferably metallic such as stainless steel for example a grade available as 304 VSS -
- the helix wire is of circular cross section although other cross sections can be used, such as rectangular, as shown in Figures 2 to 4.
- the turns of the helical coil 5 are conveniently spaced apart.
- a cylindrical helix wire about 0.05mm (0.002") diameter can have a pitch of about 0.01mm (0.004").
- the first tubular member is received in a second tubular member 10.
- the second tubular member 10 may be bonded to the first tubular member but this is not essential and, as mentioned below, it may desirably not be so bonded.
- Second tubular member 10 comprises heat shrunk material such as heat shrink PTFE (polytetrafluoroethylene), polyester or FEP.
- the tip 20 of the catheter tapers inwardly.
- Helical coil 5 may not extend to the tip 20 and preferably does not do so. A reason for this will be explained hereinafter.
- a hub 30 such as a luer hub can be fitted to the end of the catheter opposite to the tip 20.
- a needle (not shown) can be fitted to the tip of the catheter.
- the flexibility of the catheter can be varied by, for example, varying the stiffness of the helical coil. Those skilled will have little difficulty in varying the flexibility of the helical coil, for example, by varying the material of which it is made or the thickness of the wire.
- the flexibility of the catheter can be varied in other ways such as varying the thickness or the nature of the heat flowed plastics material.
- Mandrel 100 is conveniently a rigid metallic material, e.g. a stainless steel wire.
- a release layer 101 such as silicone oil or a PTFE coating is present on the mandrel 100.
- Silicone oil is satisfactory since it is available in medical grades and thus it may not matter if slight traces remain after processing.
- a PTFE coating is preferred because of its chemical inertness.
- a PTFE coating may be deposited onto the surface of the mandrel. Alternatively, a PTFE tube may be snugly fitted onto the mandrel.
- a helical coil 5 as described previously is slid onto the mandrel 100 over the release layer.
- the internal diameter of the helical coil 5 is preferably slightly larger than the external diameter of the mandrel 100. In an example the mandrel was about 0.05mm (0.002") less in diameter than the internal diameter of the coil 5.
- a tube of plastics material 110 flowable at a first, elevated, temperature is slid over the helical coil. In many cases the heat flowable material 110 is the same as the heat flowed plastics of matrix 4. It is not essential however since material 110 could be a material which undergoes a chemical or physical transformation on heating so that it is not heat flowable on a further heating. Suitable materials include an FEP, polyethylene and poiyurethane.
- a second tube 120 of heat shrinkable plastics material is then slid over the first tube to make an assembly.
- the second tube is heat shrinkable at a temperature greater than a temperature at which the first tube is flowable, and does not flow at the temperature at which the first tube begins to flow. It will be appreciated that the coil is a relatively snug fit on the mandrel and similarly, the first tube fits relatively closely to the helical coil, while the second tube also fits closely to the first tube. For better clarity, the distances between the various components are exaggerated in Figures 2 to 4.
- the helical coil does not extend to the tip of the tubes. Where the coil does not extend to the tip of the tubes a tapered portion is formed. This taper, which may be trimmed during a finishing step, facilitates introduction of the catheter into the body.
- the assembly of mandrel, coil, first and second tubes is then heated, e.g. in an oven or by means of a radiant heating element or elements directing heat onto the outer surface of the second tube 120.
- the radiant heater is annular and the assembly in advanced at an appropriate speed through the annulus of the heater. The duration of heating is sufficient to ensure that the entire assembly is heated to the same temperature, such temperature being high enough to cause the material of the first tube to flow and the material of the second to shrink.
- the mandrel may be removed, preferably after the heating, and the release layer or coating remains on the surface of the mandrel. As the assembly is heated, the first tube softens and becomes heat flowable.
- the second tube then shrinks forcing the heat flowable material into the gaps between the turns of the helical coil 5 at least partially enveloping it.
- the heat flowable material substantially completely envelopes the helical coil.
- the flowable material flows between the mandrel and the coil.
- a circular cross-section helix wire is preferred since there is a smaller area of wire adjacent to the mandrel than if say a square cross section wire of the same cross- sectional area were used. In positions along the length of the assembly where the coil is not present, greater shrinkage takes place and this allows formation of the preferred tapered tip 20.
- a hollow needle may be fitted to the tip. This step may be a part of the process of manufacturing the catheter.
- the needle may be fitted temporarily in place of the mandrel and the end of the tube further heat shrunk onto an end of the needle.
- the precise temperature to which the assembly should be heated depends on the nature of the polymers.
- the first tube is generally flowable at a temperature in the range of 100 to 300°C.
- the second tube is generally selected to be heat shrinkable at a temperature about 50 to 100°C higher than the temperature at which the plastics material of the first tube becomes flowable. Typically therefore the second tube heat shrinks at a temperature in the range 150 to 350°C. Temperatures higher than 350°C are generally not preferred.
- the mandrel 100 if present can be removed and the catheter processed further for example in conventional manner by attaching, e.g. by welding, adhesively bonding or insert moulding the catheter to the hub 30.
- the second tube may be removed, leaving the coil substantially embedded in the wall of the first tube. This results in a reinforced catheter having a smaller overall diameter.
- the second tube is conveniently removed, e.g. by slitting and peeling it away from the first tube, while the first tube is still supported on the mandrel.
- the mandrel may then be removed.
- a reinforced catheter as produced by this method is shown in Figure 5.
- Catheters manufactured in accordance with this invention are particularly useful for introducing sensors, e.g. optical sensors, into a patient's blood vessel for monitoring parameters such as blood oxygen, CO2 and pH.
- the reinforced catheter protects the delicate sensor while retaining the necessary flexibility for passing the catheter into a blood vessel.
- Examples of typical optical sensors are those manufactured by Diametrics Medical Limited of Short Street. High Wycombe, England under the trade mark 'Paratrend', and described in US Patents Nos. 4889407 and 5262037, the disclosure of which is specifically incorporated by reference.
- the outer layer is stripped away once the heat flowing has occurred.
- a preferred technique is to provide a stainless steel mandrel covered with a thin PTFE tube and to support the helical spring on such a mandreL, while forming the reinforced catheter comprising a first, heat-flowable tube, and a second heat-shrinkable tube. After the heat-shrinking step, the mandrel is removed and replaced with an uncoated stainless steel wire. Using this wire as a support, the heat-shrinkable second tube is slit and peeled away to leave the first tube encapsulating the helical spring.
- a further tube is provided between the helical coil and the mandrel and is chosen to bond with the further tube. This helps to ensure that the coil is encapsulated by plastics materials. Poiyurethane, polyethylene or PTFE may be used for the further tube. It may be preferable for the further tube and the first tube to be of the same or similar polymer composition.
- PTFE and FEP tubing available from Zeus, Orangebury, South Carolina, USA, the PTFE shrinks at a temperature in the range 335-343°C (635-650°F) and the FEP flows at 260-277°C (500-530°F).
- the first tube may be found to adhere to parts of the mandrel despite the presence of a release oil. This may be due to surface scratches on the mandrel.
- the formed catheter can be removed from the mandrel by clamping the mandrel at one end (e.g. in jaws of a vice) and gripping the catheter at the other, while twisting it so that the coil tends to open up. This action effectively breaks any bond between the inner surface of the catheter and the mandrel.
- the reinforced catheters of this invention may be introduced into a blood vessel using the hollow needle and wire technique, known as the Seldinger technique.
- the Seldinger technique known as the Seldinger technique.
- a system transition from a smaller to a larger system may be adopted, such as the system described in US Patent No. 4,650,472, the disclosure of which is specifically incorporated herein by reference.
Abstract
Description
Claims
Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP2000553163A JP2002517291A (en) | 1998-06-09 | 1999-06-08 | Double wall catheter and method of manufacturing the same |
EP99955439A EP1083957A1 (en) | 1998-06-09 | 1999-06-08 | Double walled catheter and method of manufacture |
GB0025549A GB2353839B (en) | 1998-06-09 | 1999-06-08 | Double walled catheter and method of manufacture |
KR1020007013960A KR20010034907A (en) | 1998-06-09 | 1999-06-08 | Double walled catheter and method of manufacture |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US9393498A | 1998-06-09 | 1998-06-09 | |
US09/093,934 | 1998-06-09 |
Publications (1)
Publication Number | Publication Date |
---|---|
WO1999064097A1 true WO1999064097A1 (en) | 1999-12-16 |
Family
ID=22241784
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/GB1999/001814 WO1999064097A1 (en) | 1998-06-09 | 1999-06-08 | Double walled catheter and method of manufacture |
Country Status (5)
Country | Link |
---|---|
EP (1) | EP1083957A1 (en) |
JP (1) | JP2002517291A (en) |
KR (1) | KR20010034907A (en) |
GB (1) | GB2353839B (en) |
WO (1) | WO1999064097A1 (en) |
Cited By (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO2002011806A1 (en) * | 2000-08-03 | 2002-02-14 | Boston Scientific Limited | Reinforced catheter and method of manufacture |
WO2003035160A1 (en) * | 2001-10-23 | 2003-05-01 | Novarix Ltd | A device for supporting and stabilising a tubing for fluid transport and such a tubing |
WO2006096314A2 (en) * | 2005-03-04 | 2006-09-14 | Gore Enterprise Holdings, Inc. | Polymer shrink tubes and novel uses therefor |
US9901661B2 (en) | 2014-06-06 | 2018-02-27 | Zeus Industrial Products, Inc. | Peelable heat-shrink tubing |
Families Citing this family (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
CN105396215A (en) | 2010-08-13 | 2016-03-16 | 导管治疗有限公司 | A Catheter Sheath And A Method Of Manufacturing |
JP2012071038A (en) * | 2010-09-29 | 2012-04-12 | Kaneka Corp | Coil processing device, coil processing method, and medical tube manufacturing method |
Citations (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4650472A (en) | 1985-08-30 | 1987-03-17 | Cook, Incorporated | Apparatus and method for effecting percutaneous catheterization of a blood vessel using a small gauge introducer needle |
US4889407A (en) | 1988-12-02 | 1989-12-26 | Biomedical Sensors Limited | Optical waveguide sensor and method of making same |
US5180376A (en) * | 1990-05-01 | 1993-01-19 | Cathco, Inc. | Non-buckling thin-walled sheath for the percutaneous insertion of intraluminal catheters |
US5262037A (en) | 1992-05-22 | 1993-11-16 | Biomedical Sensors, Ltd. | Electrochemical sensor |
US5669920A (en) * | 1993-07-09 | 1997-09-23 | Devices For Vascular Intervention, Inc. | Atherectomy catheter |
US5676784A (en) * | 1995-03-15 | 1997-10-14 | Abbott Laboratories | Method of fabricating a heater coil for a catheter used to monitor cardiac output |
WO1997037713A1 (en) * | 1996-04-05 | 1997-10-16 | Csaba Truckai | Thin-walled and braid-reinforced catheter |
WO1997048437A1 (en) * | 1996-06-21 | 1997-12-24 | Medtronic, Inc. | Reinforced catheter body and method for its fabrication |
-
1999
- 1999-06-08 WO PCT/GB1999/001814 patent/WO1999064097A1/en not_active Application Discontinuation
- 1999-06-08 JP JP2000553163A patent/JP2002517291A/en not_active Withdrawn
- 1999-06-08 KR KR1020007013960A patent/KR20010034907A/en not_active Application Discontinuation
- 1999-06-08 EP EP99955439A patent/EP1083957A1/en not_active Withdrawn
- 1999-06-08 GB GB0025549A patent/GB2353839B/en not_active Expired - Fee Related
Patent Citations (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4650472A (en) | 1985-08-30 | 1987-03-17 | Cook, Incorporated | Apparatus and method for effecting percutaneous catheterization of a blood vessel using a small gauge introducer needle |
US4889407A (en) | 1988-12-02 | 1989-12-26 | Biomedical Sensors Limited | Optical waveguide sensor and method of making same |
US5180376A (en) * | 1990-05-01 | 1993-01-19 | Cathco, Inc. | Non-buckling thin-walled sheath for the percutaneous insertion of intraluminal catheters |
US5262037A (en) | 1992-05-22 | 1993-11-16 | Biomedical Sensors, Ltd. | Electrochemical sensor |
US5669920A (en) * | 1993-07-09 | 1997-09-23 | Devices For Vascular Intervention, Inc. | Atherectomy catheter |
US5676784A (en) * | 1995-03-15 | 1997-10-14 | Abbott Laboratories | Method of fabricating a heater coil for a catheter used to monitor cardiac output |
WO1997037713A1 (en) * | 1996-04-05 | 1997-10-16 | Csaba Truckai | Thin-walled and braid-reinforced catheter |
WO1997048437A1 (en) * | 1996-06-21 | 1997-12-24 | Medtronic, Inc. | Reinforced catheter body and method for its fabrication |
Cited By (13)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6669886B1 (en) | 2000-08-03 | 2003-12-30 | Scimed Life Systems, Inc. | Reinforced catheter and method of manufacture |
WO2002011806A1 (en) * | 2000-08-03 | 2002-02-14 | Boston Scientific Limited | Reinforced catheter and method of manufacture |
US7198066B2 (en) | 2001-10-23 | 2007-04-03 | Novarix Ltd., Oxford Centre For Innovation | Device for supporting and stabilising a tubing for fluid transport and such a tubing |
WO2003035160A1 (en) * | 2001-10-23 | 2003-05-01 | Novarix Ltd | A device for supporting and stabilising a tubing for fluid transport and such a tubing |
AU2006221013B2 (en) * | 2005-03-04 | 2010-07-29 | W. L. Gore & Associates, Inc. | Polymer shrink tubes and novel uses therefor |
WO2006096314A3 (en) * | 2005-03-04 | 2007-01-11 | Gore Enterprise Holdings Inc | Polymer shrink tubes and novel uses therefor |
WO2006096314A2 (en) * | 2005-03-04 | 2006-09-14 | Gore Enterprise Holdings, Inc. | Polymer shrink tubes and novel uses therefor |
EP2311507A1 (en) * | 2005-03-04 | 2011-04-20 | Gore Enterprise Holdings, Inc. | Polymer shrink tubes and novel uses therefor |
US8252219B2 (en) | 2005-03-04 | 2012-08-28 | W. L. Gore & Associates, Inc. | Polymer shrink tubes and novel uses therefor |
EP2762176A3 (en) * | 2005-03-04 | 2014-08-13 | Gore Enterprise Holdings, Inc. | Polymer shrink tubes and novel uses therefor |
US9320831B2 (en) | 2005-03-04 | 2016-04-26 | W. L. Gore & Associates, Inc. | Polymer shrink tubes and novel uses therefor |
US9901661B2 (en) | 2014-06-06 | 2018-02-27 | Zeus Industrial Products, Inc. | Peelable heat-shrink tubing |
US10434222B2 (en) | 2014-06-06 | 2019-10-08 | Zeus Industrial Products, Inc. | Peelable heat-shrink tubing |
Also Published As
Publication number | Publication date |
---|---|
GB2353839A (en) | 2001-03-07 |
JP2002517291A (en) | 2002-06-18 |
GB2353839B (en) | 2003-04-16 |
GB0025549D0 (en) | 2000-11-29 |
EP1083957A1 (en) | 2001-03-21 |
KR20010034907A (en) | 2001-04-25 |
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