US20010016705A1 - Shaft for medical catheters - Google Patents
Shaft for medical catheters Download PDFInfo
- Publication number
- US20010016705A1 US20010016705A1 US09/382,610 US38261099A US2001016705A1 US 20010016705 A1 US20010016705 A1 US 20010016705A1 US 38261099 A US38261099 A US 38261099A US 2001016705 A1 US2001016705 A1 US 2001016705A1
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- United States
- Prior art keywords
- catheter
- coating
- marker
- shaft
- tubular body
- 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.)
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Classifications
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- 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
- A61M25/10—Balloon catheters
- A61M25/1027—Making of balloon catheters
- A61M25/1036—Making parts for balloon catheter systems, e.g. shafts or distal ends
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- 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
- A61M25/10—Balloon catheters
- A61M25/104—Balloon catheters used for angioplasty
-
- 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
- A61M2025/0046—Coatings for improving slidability
-
- 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
- A61M25/10—Balloon catheters
- A61M2025/1043—Balloon catheters with special features or adapted for special applications
- A61M2025/1079—Balloon catheters with special features or adapted for special applications having radio-opaque markers in the region of the balloon
Definitions
- the present invention relates generally to surgical device design and fabrication and, more particularly, to a shaft for medical catheters.
- Previously known catheters are of complex construction, requiring expensive manufacturing steps and construction of great precision to navigate the tortuous pathways of a vessel network.
- a catheter provides inflation fluid to a balloon
- a small notch is typically provided in the catheter tube to allow fluid to pass from a lumen within the tube to the balloon.
- the conventional method for manufacturing this notch is with a laser, which is expensive and often cannot be done in-house.
- use of a laser creates a heat-affected zone which can lead to fracture of the notch.
- the heat from the laser may cause deformation of the material. This is especially problematic when a straight catheter made of a nickel-titanium alloy is desired. Because the properties of NiTi alloys are extremely temperature sensitive, laser notching may cause buckling or unwanted curvature in the material. Accordingly, there is a need for a notch-forming process which will not cause damage to the material.
- a radiopaque marker is often necessary to identify a specified location on the catheter.
- markers are typically placed on the catheter tube near the location of a distal balloon.
- visibility problems often arise with such markers because they are typically made small in order to allow the aspiration catheter to be passed over the marker as it extends towards the distal balloon. Accordingly, there is a need for balloon catheters having markers which can better identify the location of a balloon while inside a blood vessel.
- a small notch is fabricated into a catheter tube by a nonlaser process such as electric discharge machining (EDM) or mechanical grinding.
- EDM electric discharge machining
- This notch in the catheter tube is necessary for fluid communication between the catheter lumen and a balloon or other element in communication with the tube.
- Use of a nonlaser process reduces the costs of fabrication while ensuring a high degree of structural integrity.
- a method is provided to produce a thinner coating on a catheter shaft to reduce friction with vessel walls.
- the catheter is sputter coated with Teflon or similar material to produce a nonuniform coating.
- This nonuniform coating may extend 360 degrees around the catheter tube, and may even provide a coating of less than 360 degrees while still maintaining good lubricity.
- a catheter wire or tube is provided with a radiopaque marker which is more visible and is more effective at identifying the location of a balloon on the catheter.
- the marker is moved closer to a distal balloon by placing it within an adhesive taper adjacent the balloon.
- the marker can be made larger and more visible without obstructing the placement of an aspiration catheter or other type of catheter over the catheter wire or tube.
- the marker in being placed inside the taper and closer to the balloon can act as a stopper to the aspiration catheter and prevent damage to the balloon.
- FIG. 1 is a side view of the catheter of the present invention.
- FIG. 2 is a longitudinal cross-sectional view of the distal end of a catheter having the improvements of the present invention.
- FIG. 3 is an enlarged cross-sectional view along area 3 - 3 of FIG. 2.
- FIG. 4A is a cross-sectional view along line 4 - 4 of FIG. 1 showing a nonuniform coating on the catheter.
- FIG. 4B is a cross-sectional view along line 4 - 4 of FIG. 1 showing an alternate embodiment of a nonuniform coating on the catheter.
- FIG. 1 there is depicted a catheter 10 incorporating the improvements of the present invention.
- the improvements of the present invention are depicted and discussed in the context of being part of a simple occlusive device having a single lumen, it should be appreciated that the present invention is applicable to more complex occlusive devices having structures and functionalities not discussed herein.
- the present inventors contemplate that the improvements of the present invention may be used in occlusive devices functioning as anchorable guide wires or filters.
- the improvements of the present invention are also applicable to catheters having other types of balloons, such as latex or silicone, or to catheters having dilatation balloons, made of materials such as polyethylene terephthalate.
- the improvements of the present invention may also be adapted to other types of catheters used in drug delivery or radiation therapy, such as irrigation catheters, and to catheters having no balloon at all.
- irrigation catheters used in drug delivery or radiation therapy
- catheters having no balloon at all such as irrigation catheters, and to catheters having no balloon at all.
- Catheter 10 generally comprises an elongate flexible shaft or tubular body 12 extending between a proximal control end 14 , corresponding to a proximal section of tubular body 12 , and a distal functional end 16 , corresponding to a distal section of tubular body 12 .
- Tubular body 12 has a central lumen 18 which extends between ends 14 and 16 .
- An inflation port 20 is provided on tubular body 12 near the proximal end 14 .
- Inflation port 20 is in fluid communication with lumen 18 , such that fluid passing through inflation port 20 into or out of lumen 18 may be used to inflate or deflate inflation balloons in communication with lumen 18 .
- Lumen 18 is sealed fluid tight at distal end 16 .
- Inflation port 20 may be similar to existing female luer lock adapters or would be a removable valve at the end, as disclosed in assignee's co-pending application entitled LOW PROFILE CATHETER VALVE AND INFLATION ADAPTER, application Ser. No. 08/975,723 filed Nov. 20, 1997, the entirety of which is incorporated by reference.
- tubular body 12 may be varied considerably depending upon the desired application.
- tubular body 12 is comprised of a hollow hypotube having a length in the range of from about 160 to about 320 centimeters with a length of about 180 centimeters being optimal for a single operator device and 300 centimeters for over the wire applications.
- the catheter 10 may comprise a solid shaft rather than a hollow hypotube.
- Tubular body 12 generally has a circular cross-sectional configuration with an outer diameter within the range of from about 0.008 inches to 0.14 inches.
- the outer diameter of tubular body 12 ranges from 0.010 inches to 0.038 inches, and preferably is about 0.014 to 0.018 inches in outer diameter or smaller.
- Noncircular cross-sectional configurations of lumen 18 can also be adapted for use with the present invention. For example, triangular, rectangular, oval, and other noncircular cross-sectional configurations are also easily incorporated for use with the present invention, as will be appreciated by those of skill in the art.
- Tubular body 12 has sufficient structural integrity, or “pushability,” to permit catheter 10 to be advanced through vasculature to distal arterial locations without buckling or undesirable kinking of tubular body 12 . It is also desirable for tubular body 12 to have the ability to transmit torque, such as in those embodiments where it may be desirable to rotate tubular body 12 after insertion into a patient.
- a variety of biocompatible materials known by those of skill in the art to possess these properties and to be suitable for catheter manufacture, may be used to produce tubular body 12 .
- tubular body 12 may be made of stainless steel such as Elgiloy (TM), or may be made of polymeric materials such as nylon, polyimide, polyamides, polyethylene or combinations thereof.
- tubular body 12 out of an alloy of titanium and nickel, commonly referred to as nitinol.
- the nitinol alloy used to form tubular body 12 is comprised of about 50.8% nickel and the balance titanium, which is sold under the trade name Tinel (TM) by Memry Corporation.
- Tinel Tinel
- an expandable member such as an inflatable balloon 22 is mounted on tubular body 12 .
- Balloon 22 may be secured to tubular body 12 by any means known to those skilled in the art, such as adhesives or heat bonding.
- balloon 22 is a compliant balloon formed out of a material comprising a block polymer of styrene-ethylene-butylene-styrene (SEBS).
- SEBS block polymer of styrene-ethylene-butylene-styrene
- balloon 22 has a proximal end 24 and a distal end 26 which are both secured to the outer surface of tubular body 12 .
- Balloon 22 may be secured to the tubular body 12 by any means known to those of skill in the art, such as adhesives or heat bonding.
- a notch 36 is provided in the tubular body 12 , as shown on the back side of tubular body 12 in FIG. 2, within the working length of the balloon to provide fluid communication between the lumen 18 and the balloon 22 .
- a core wire 38 is provided at the distal end of the tubular body 12 , inserted into the lumen 18 so that part of the core wire 38 is visible through the notch 36 .
- Coil 40 surrounds the core wire 38 and is soldered at a distal end into a rounded tip 42 .
- the core wire 38 is secured within the lumen 18 of tubular body 12 by a combination of adhesive bonding and crimping at points 44 and 46 of the tubular body 12 .
- Tapers 48 and 50 are shown at the proximal and distal ends of the balloon 22 , respectively.
- a radiopaque marker 52 is located within the proximal taper 48 .
- the core wire 38 and the coil 40 are formed into a subassembly prior to attachment to tubular body 12 .
- a proximal end of core wire 38 is inserted into tubular body 12 at distal end 54 .
- Two crimps 44 and 46 are provided near the distal end 54 of the tubular body 12 to secure the core wire 38 to the tubular body.
- the crimps are preferably located in a location between the notch 36 and the distal end 54 of the tubular body 12 .
- the crimps are preferably located a distance 0.5 to 1.5 mm apart, and more preferably, about 1.0 mm apart.
- the more distal crimp 46 preferably is located about 0.5 mm from the distal end 54 of tubular body 12 . Further details are disclosed in the above-referenced application CORE WIRE WITH SHAPEABLE TIP (Attorney Docket PERCUS.053A), application Ser. No. ______, filed on the same date herewith.
- the notch 36 shown in FIG. 2 is formed by a nonlaser process.
- the process used is electric discharge machining (EDM).
- EDM electric discharge machining
- This method allows removal of metal by a series of rapidly recurring electrical discharges between an electrode (the cutting tool) and the workpiece in the presence of a liquid (usually hydrocarbon dielectric).
- a liquid usually hydrocarbon dielectric.
- the notch 36 preferably has a length between 0.001 and 0.005 inches and a width between 0.001 and 0.005 inches, depending on the working length of the balloon 22 and the diameter of the tubular body 12 . As shown in FIG.
- the notch 36 when the distance between the inner surfaces of the adhesive stops 32 and 34 is 4 mm and the outer diameter of the tubular body 12 is 0.0132 inches, the notch 36 preferably has a length of 1.5 mm and a width of 0.003 inches.
- the notch 36 may be centered within the working length of the balloon, such that the distance between the ends of the notch and each of the adhesive stops 32 and 34 is the same.
- the location of the notch 36 may be shifted towards distal end 54 of the tubular body. In FIG. 2, where the distance between adhesive stops 32 and 34 is 4 mm, the core wire 38 extends 0.5 mm into the notch 36 .
- the notch 36 is 1.5 mm long, with the proximal end 56 of the notch 36 located a distance 1.5 mm from the first adhesive stop 32 , and the distal end 58 of the notch 36 located 1 mm from the second adhesive stop 34 .
- EDM EDM with a 0.0055 ⁇ 0.0005 inch electrode
- a current of 0.5 amps is applied, with an on time of 6 seconds and an off time of 50 seconds.
- EDM processing of the notch has been described with respect to specific parameters, it should be recognized that other parameters as well may be used for the EDM.
- EDM may be used not only for fabrication of a distal notch to inflate a balloon, but also for a notch such as inflation port 20 at the proximal end of the tubular body as shown in FIG. 1, or other types of notches that may be provided for a medical catheter.
- the shaft or tubular body 12 is sputter-coated with a polymeric material to reduce friction between the catheter and blood vessels and produce a lubricious, nonuniform coating on the tubular body 12 .
- nonuniform refers either to a coating that is variable in thickness along the circumference or length of the body 12 , or to a coating which covers the body 12 in some areas but not at all in others.
- a coating 60 is applied to the tubular body 12 between a proximal marker 62 and the balloon 22 . The coating begins at a distance preferably within about 5 mm of the marker 62 , and more preferably within about 2 mm.
- the coating 60 terminates preferably within about 1 cm of the proximal taper 48 .
- Preferred coating materials include polytetrafluoroethylene (TFE), with Teflon being a desired material for the coating 60 .
- TFE polytetrafluoroethylene
- Teflon Teflon
- FIGS. 4A and 4B a nonuniform coating 60 adds very little dimension to the tubular body 12 .
- FIG. 4A shows one embodiment where the coating 60 is thin with a variable thickness that covers substantially the entire circumference of the tubular body 12 .
- FIG. 4B shows another embodiment where the coating 60 is thin but does not coat the entire circumference of tubular body 12 . Thicknesses in the range of about 0.001 to about 0.0035 inches are preferred.
- the coating 60 has a thickness of no greater than about 0.01 inches, and more preferably, the coating thickness is no greater than about 0.0035 inches.
- the surface of the tubular body 12 is first cleaned.
- Preferable cleaning methods are by preparing a cleaning solvent blend using a 1:1 (by volume) mixture of acetone and isopropyl alcohol.
- the tubular body 12 may be cleaned by wiping the body with a lint-free towel or cloth wetted by this solvent blend. After the solvent wipe, the tubular body 12 is heat cleaned in an oven for 15 minutes at 540° F.
- the Teflon coating solution may be Xylan 1006/870 Black Teflon coating as obtained from Whitford Corporation.
- the coating can be mixed with a thinner such as thinner #99B from Whitford Corporation.
- the coating solution is first mixed well in a container using a mechanical stirrer for about 5 to 10 minutes to remove residue and Teflon particles from the bottom of the container.
- About 80 parts by volume of the coating solution is mixed with about 20 parts by volume of the thinner with a mechanical stirrer until the blend is uniform to achieve 0.0035 inch thickness.
- This blend is filtered using a cone type coarser filter paper to remove lumps. After completing these steps, the coating solution is ready to spray.
- the coating is produced on the tubular body by a spray gun, preferably with an agitating pressure pot, although a spray gun without an agitating pressure pot may be used.
- the spraying process of the present invention preferably produces a nonuniform Teflon coating 360 degrees around the tubular body and extending continuously along the length of the tubular body 12 .
- the trigger can be selectively depressed and released, or depressed with various degrees of pressure, as the gun passes from left to right over a portion of the tubular body. This process is repeated as the tubular body is rotated and a coating is applied 360 degrees around the tubular body.
- Coating on the tubular body by the spray gun can also be adjusted by controlling the flow rate of the spray exiting the gun. Moreover, the motion of the gun over the body allows control of the thickness and uniformity of the coating. These factors allow the coating 60 to be a thin, nonuniform coating covering substantially all of the tubular body, as shown in FIG. 4A.
- the profile of the catheter can be reduced even further by spraying less than 360 degrees around the tubular body 12 , as shown in FIG. 4B.
- the nonuniformity of the coating thus, results from the tubular body 12 having portions that are coated with the polymer and other portions having no coating at all.
- the degree of nonuniformity depends on how the trigger of the spray gun is selectively activated and deactivated. Other methods to produce nonuniformity on the tubular body 12 , such as masking portions of tubular body 12 , may also be used.
- the nonuniformity may result from the coating not being sprayed continuously over the circumference and/or length of the body.
- the coating should be flashed off to avoid any blistering.
- the coated tubular bodies are flashed off in an oven at 200° F. for 15 minutes. Then, the tubular body is cured.
- a curing temperature of about 540° F. is used in order to maintain the heat treated superelastic properties of NiTi. The curing step takes about one-half hour.
- parts of the tubular body may be stripped to remove the coating from undesired areas. For instance, at the location of the proximal marker 62 shown in FIG. 1, no coating is desired. Suitable means for stripping include an abrasive and a razor blade, as well as other stripping means known to those skilled in the art.
- a tubular marker 52 is located within an adhesive taper 48 adjacent the balloon 22 .
- the marker 52 is shown in the form of a tube, it will be appreciated by those skilled in the art that markers of other shapes may be used as well.
- the marker is first slid over the coil 40 and core wire 38 and over the distal tip of the tubular body 12 past the inflation notch 36 so that it is out of the way for balloon bonding.
- Adhesive stops 32 and 34 and the balloon 22 are then mounted to the tubular body 12 using adhesives or other means known to those skilled in the art.
- the marker 52 is slid towards the balloon 22 such that it is between about 0.5 and 3 mm from the proximal end of the balloon. More preferably, the marker 52 is located within about 1.0 mm from the proximal end 24 of the balloon 22 . In the preferred embodiment shown in FIG. 2, the marker 52 is located about 0.75 mm from the balloon.
- the gap between the balloon 22 and the marker 52 is filled with an adhesive material taper 48 .
- a cyanoacrylate adhesive such as LOCTITE 4011 is used. However, as will be appreciated by those of skill in the art, other adhesives may be used.
- the taper 48 also extends from the proximal end 64 of the marker to point 66 on the tubular body 12 , as well as from the proximal end 24 of balloon 22 to proximal end 64 of marker 52 .
- the marker is placed within the adhesive taper 48 of the balloon 22 , the marker can be made larger and closer to the balloon, thereby increasing visibility without obstructing advancement of an aspiration catheter or the like when the tubular body 12 is used as a guidewire. Further details regarding an aspiration catheter are disclosed in assignee's co-pending application entitled ASPIRATION CATHETER, application Ser. No. 08/813,308, filed Mar. 6, 1997, the entirety of which is hereby incorporated by reference.
- the marker preferably has an outer diameter of at least about 0.02 inches. More preferably, the marker 52 has an inner diameter of about 0.017 inches and an outer diameter of about 0.024 inches.
- the proximal cyanoacrylate balloon taper 48 is preferably about 4 mm long, extending from point 24 on the balloon 22 to point 66 on the tubular body.
- the marker taper, extending from point 24 to distal point 68 on marker 52 is preferably about 0.75 mm long.
Abstract
Several improvements are provided in the design of a catheter shaft to reduce costs and improve performance. In one aspect, a small notch is fabricated into a catheter tube by a nonlaser process such as electric discharge machining (EDM) or mechanical grinding. This notch in the catheter tube is necessary for fluid communication between the catheter lumen and a balloon or other element in communication with the tube. Use of a nonlaser process reduces the costs of fabrication while ensuring a high degree of structure integrity. In another aspect, a method is provided to produce a nonuniform polymer coating on a catheter shaft to reduce friction and to maintain a catheter with a low profile. In another aspect, the catheter is provided with a radiopaque marker which is more visible and is more effective at identifying the location of a balloon. The marker is moved closer to a distal balloon by placing it within an adhesive taper adjacent the balloon.
Description
- 1. Field of the Invention
- The present invention relates generally to surgical device design and fabrication and, more particularly, to a shaft for medical catheters.
- 2. Background of the Invention
- Medical catheters, such as balloon catheters, have been proven efficacious in treating a wide variety of blood vessel disorders. Moreover, these types of catheters have permitted clinicians to treat disorders with minimally invasive procedures that, in the past, would have required complex and perhaps life threatening surgeries. For example, balloon angioplasty is now a common procedure to alleviate stenotic lesions (i.e., clogged arteries) in blood vessels, thereby reducing the need for heart bypass operations.
- Previously known catheters are of complex construction, requiring expensive manufacturing steps and construction of great precision to navigate the tortuous pathways of a vessel network. For instance, when a catheter provides inflation fluid to a balloon, a small notch is typically provided in the catheter tube to allow fluid to pass from a lumen within the tube to the balloon. The conventional method for manufacturing this notch is with a laser, which is expensive and often cannot be done in-house. Further, use of a laser creates a heat-affected zone which can lead to fracture of the notch. Moreover, the heat from the laser may cause deformation of the material. This is especially problematic when a straight catheter made of a nickel-titanium alloy is desired. Because the properties of NiTi alloys are extremely temperature sensitive, laser notching may cause buckling or unwanted curvature in the material. Accordingly, there is a need for a notch-forming process which will not cause damage to the material.
- Further, profile is often a concern for catheters because of the small space in which the catheters will be inserted. In addition, because catheters must be passed through a tortuous blood vessel network to reach the intended treatment site, it is desirable that the catheters be substantially frictionless to reduce harmful contact with blood vessel walls. Catheters therefore are generally provided with a coating that will increase lubricity of the catheter. These coatings add additional, undesired size to the catheter. Thus, there is a need for a substantially frictionless catheter surface which does not add significant profile to a catheter tube.
- In navigating the pathways of a vessel network, a radiopaque marker is often necessary to identify a specified location on the catheter. Such markers are typically placed on the catheter tube near the location of a distal balloon. However, in medical devices employing aspiration catheters and the like, visibility problems often arise with such markers because they are typically made small in order to allow the aspiration catheter to be passed over the marker as it extends towards the distal balloon. Accordingly, there is a need for balloon catheters having markers which can better identify the location of a balloon while inside a blood vessel.
- The present invention addresses the needs raised above by providing several improvements in the design of a shaft for medical catheters. In one aspect, a small notch is fabricated into a catheter tube by a nonlaser process such as electric discharge machining (EDM) or mechanical grinding. This notch in the catheter tube is necessary for fluid communication between the catheter lumen and a balloon or other element in communication with the tube. Use of a nonlaser process reduces the costs of fabrication while ensuring a high degree of structural integrity.
- In another aspect of the present invention, a method is provided to produce a thinner coating on a catheter shaft to reduce friction with vessel walls. To maintain a surface with a low friction coefficient while keeping the profile of the catheter low, the catheter is sputter coated with Teflon or similar material to produce a nonuniform coating. This nonuniform coating may extend 360 degrees around the catheter tube, and may even provide a coating of less than 360 degrees while still maintaining good lubricity.
- In yet another aspect, a catheter wire or tube is provided with a radiopaque marker which is more visible and is more effective at identifying the location of a balloon on the catheter. The marker is moved closer to a distal balloon by placing it within an adhesive taper adjacent the balloon. By placing the marker in the taper, the marker can be made larger and more visible without obstructing the placement of an aspiration catheter or other type of catheter over the catheter wire or tube. Specifically, the marker in being placed inside the taper and closer to the balloon can act as a stopper to the aspiration catheter and prevent damage to the balloon.
- FIG. 1 is a side view of the catheter of the present invention.
- FIG. 2 is a longitudinal cross-sectional view of the distal end of a catheter having the improvements of the present invention.
- FIG. 3 is an enlarged cross-sectional view along area3-3 of FIG. 2.
- FIG. 4A is a cross-sectional view along line4-4 of FIG. 1 showing a nonuniform coating on the catheter.
- FIG. 4B is a cross-sectional view along line4-4 of FIG. 1 showing an alternate embodiment of a nonuniform coating on the catheter.
- Referring to FIG. 1, there is depicted a catheter10 incorporating the improvements of the present invention. Although the improvements of the present invention are depicted and discussed in the context of being part of a simple occlusive device having a single lumen, it should be appreciated that the present invention is applicable to more complex occlusive devices having structures and functionalities not discussed herein. For example, the present inventors contemplate that the improvements of the present invention may be used in occlusive devices functioning as anchorable guide wires or filters. In addition, the improvements of the present invention are also applicable to catheters having other types of balloons, such as latex or silicone, or to catheters having dilatation balloons, made of materials such as polyethylene terephthalate. Moreover, the improvements of the present invention may also be adapted to other types of catheters used in drug delivery or radiation therapy, such as irrigation catheters, and to catheters having no balloon at all. The manner of adapting the improvements of the present invention to these various structures and functionalities will become readily apparent to those of skill in the art in view of the description which follows.
- In FIG. 1, an occlusion balloon catheter10 is shown. Catheter 10 generally comprises an elongate flexible shaft or
tubular body 12 extending between aproximal control end 14, corresponding to a proximal section oftubular body 12, and a distalfunctional end 16, corresponding to a distal section oftubular body 12.Tubular body 12 has acentral lumen 18 which extends betweenends inflation port 20 is provided ontubular body 12 near theproximal end 14.Inflation port 20 is in fluid communication withlumen 18, such that fluid passing throughinflation port 20 into or out oflumen 18 may be used to inflate or deflate inflation balloons in communication withlumen 18.Lumen 18 is sealed fluid tight atdistal end 16.Inflation port 20 may be similar to existing female luer lock adapters or would be a removable valve at the end, as disclosed in assignee's co-pending application entitled LOW PROFILE CATHETER VALVE AND INFLATION ADAPTER, application Ser. No. 08/975,723 filed Nov. 20, 1997, the entirety of which is incorporated by reference. - The length of
tubular body 12 may be varied considerably depending upon the desired application. For example, where catheter 10 serves as a guidewire for other catheters in a conventional percutaneous transluminal coronary angioplasty procedure involving femoral artery access,tubular body 12 is comprised of a hollow hypotube having a length in the range of from about 160 to about 320 centimeters with a length of about 180 centimeters being optimal for a single operator device and 300 centimeters for over the wire applications. Alternately, for a different treatment procedure, not requiring as long a length oftubular body 12, shorter lengths oftubular body 12 may be provided. Moreover, the catheter 10 may comprise a solid shaft rather than a hollow hypotube. -
Tubular body 12 generally has a circular cross-sectional configuration with an outer diameter within the range of from about 0.008 inches to 0.14 inches. In many applications where catheter 10 is to be used as a guidewire for other catheters, the outer diameter oftubular body 12 ranges from 0.010 inches to 0.038 inches, and preferably is about 0.014 to 0.018 inches in outer diameter or smaller. Noncircular cross-sectional configurations oflumen 18 can also be adapted for use with the present invention. For example, triangular, rectangular, oval, and other noncircular cross-sectional configurations are also easily incorporated for use with the present invention, as will be appreciated by those of skill in the art. -
Tubular body 12 has sufficient structural integrity, or “pushability,” to permit catheter 10 to be advanced through vasculature to distal arterial locations without buckling or undesirable kinking oftubular body 12. It is also desirable fortubular body 12 to have the ability to transmit torque, such as in those embodiments where it may be desirable to rotatetubular body 12 after insertion into a patient. A variety of biocompatible materials, known by those of skill in the art to possess these properties and to be suitable for catheter manufacture, may be used to producetubular body 12. For example,tubular body 12 may be made of stainless steel such as Elgiloy (TM), or may be made of polymeric materials such as nylon, polyimide, polyamides, polyethylene or combinations thereof. In one preferred embodiment, the desired properties of structural integrity and torque transmission are achieved by formingtubular body 12 out of an alloy of titanium and nickel, commonly referred to as nitinol. In a preferred embodiment, the nitinol alloy used to formtubular body 12 is comprised of about 50.8% nickel and the balance titanium, which is sold under the trade name Tinel (TM) by Memry Corporation. It has been found that a catheter tubular body having this composition of nickel and titanium exhibits an improved combination of flexibility and kink resistance in comparison to other materials. Further details are disclosed in assignee's co-pending applications entitled HOLLOW MEDICAL WIRES AND METHODS OF CONSTRUCTING SAME, application Ser. No. 08/812,876, filed on Mar. 6, 1997, CATHETER BALLOON CORE WIRE, application Ser. No. 08/813,024, filed Mar. 6, 1997, and CORE WIRE WITH SHAPEABLE TIP (Attorney Docket PERCUS.053A), application Ser. No. ______, filed on the same date herewith, all of which are hereby incorporated by reference in their entirety. - As illustrated in FIG. 1, an expandable member such as an
inflatable balloon 22 is mounted ontubular body 12.Balloon 22 may be secured totubular body 12 by any means known to those skilled in the art, such as adhesives or heat bonding. In one preferred embodiment,balloon 22 is a compliant balloon formed out of a material comprising a block polymer of styrene-ethylene-butylene-styrene (SEBS). As shown in FIGS. 2 and 3,balloon 22 has aproximal end 24 and a distal end 26 which are both secured to the outer surface oftubular body 12.Balloon 22 may be secured to thetubular body 12 by any means known to those of skill in the art, such as adhesives or heat bonding. FIGS. 2 and 3 show the use ofadhesives 28 bonding the balloon at itsproximal end 24 and distal end 26, respectively, up toadhesive stops - A
notch 36 is provided in thetubular body 12, as shown on the back side oftubular body 12 in FIG. 2, within the working length of the balloon to provide fluid communication between thelumen 18 and theballoon 22. Acore wire 38 is provided at the distal end of thetubular body 12, inserted into thelumen 18 so that part of thecore wire 38 is visible through thenotch 36. Coil 40 surrounds thecore wire 38 and is soldered at a distal end into a rounded tip 42. Thecore wire 38 is secured within thelumen 18 oftubular body 12 by a combination of adhesive bonding and crimping atpoints tubular body 12.Tapers 48 and 50 are shown at the proximal and distal ends of theballoon 22, respectively. Aradiopaque marker 52 is located within the proximal taper 48. - The
core wire 38 and the coil 40 are formed into a subassembly prior to attachment totubular body 12. Once the coil 40 is attached to the core wire, a proximal end ofcore wire 38 is inserted intotubular body 12 at distal end 54. Twocrimps tubular body 12 to secure thecore wire 38 to the tubular body. The crimps are preferably located in a location between thenotch 36 and the distal end 54 of thetubular body 12. The crimps are preferably located a distance 0.5 to 1.5 mm apart, and more preferably, about 1.0 mm apart. The moredistal crimp 46 preferably is located about 0.5 mm from the distal end 54 oftubular body 12. Further details are disclosed in the above-referenced application CORE WIRE WITH SHAPEABLE TIP (Attorney Docket PERCUS.053A), application Ser. No. ______, filed on the same date herewith. - In one aspect of the present invention, the
notch 36 shown in FIG. 2 is formed by a nonlaser process. Preferably, the process used is electric discharge machining (EDM). This method allows removal of metal by a series of rapidly recurring electrical discharges between an electrode (the cutting tool) and the workpiece in the presence of a liquid (usually hydrocarbon dielectric). Using EDM, thenotch 36 can be made economically but also with great precision. Thenotch 36 preferably has a length between 0.001 and 0.005 inches and a width between 0.001 and 0.005 inches, depending on the working length of theballoon 22 and the diameter of thetubular body 12. As shown in FIG. 2, when the distance between the inner surfaces of the adhesive stops 32 and 34 is 4 mm and the outer diameter of thetubular body 12 is 0.0132 inches, thenotch 36 preferably has a length of 1.5 mm and a width of 0.003 inches. Thenotch 36 may be centered within the working length of the balloon, such that the distance between the ends of the notch and each of the adhesive stops 32 and 34 is the same. Alternatively, when thecore wire 38 extends into thelumen 18 of thetubular body 12 and is visible in thenotch 36, the location of thenotch 36 may be shifted towards distal end 54 of the tubular body. In FIG. 2, where the distance between adhesive stops 32 and 34 is 4 mm, thecore wire 38 extends 0.5 mm into thenotch 36. Thenotch 36 is 1.5 mm long, with theproximal end 56 of thenotch 36 located a distance 1.5 mm from the firstadhesive stop 32, and thedistal end 58 of thenotch 36 located 1 mm from the secondadhesive stop 34. - To manufacture the notch, preferably, an EDM with a 0.0055±0.0005 inch electrode is used. A current of 0.5 amps is applied, with an on time of 6 seconds and an off time of 50 seconds. Although the EDM processing of the notch has been described with respect to specific parameters, it should be recognized that other parameters as well may be used for the EDM. Furthermore, EDM may be used not only for fabrication of a distal notch to inflate a balloon, but also for a notch such as
inflation port 20 at the proximal end of the tubular body as shown in FIG. 1, or other types of notches that may be provided for a medical catheter. - Although fabrication of the notch has been described with reference to an EDM procedure, other nonlaser processes may be used as well. For instance, mechanical grinding is another low cost procedure for fabricating a notch that can be performed in-house.
- In another aspect of the present invention, the shaft or
tubular body 12 is sputter-coated with a polymeric material to reduce friction between the catheter and blood vessels and produce a lubricious, nonuniform coating on thetubular body 12. As used herein, “nonuniform” refers either to a coating that is variable in thickness along the circumference or length of thebody 12, or to a coating which covers thebody 12 in some areas but not at all in others. As shown in FIG. 1, a coating 60 is applied to thetubular body 12 between aproximal marker 62 and theballoon 22. The coating begins at a distance preferably within about 5 mm of themarker 62, and more preferably within about 2 mm. The coating 60 terminates preferably within about 1 cm of the proximal taper 48. Preferred coating materials include polytetrafluoroethylene (TFE), with Teflon being a desired material for the coating 60. Those skilled in the art will recognize that similar materials with high lubricity may be used. - As shown in FIGS. 4A and 4B, a nonuniform coating60 adds very little dimension to the
tubular body 12. FIG. 4A shows one embodiment where the coating 60 is thin with a variable thickness that covers substantially the entire circumference of thetubular body 12. FIG. 4B shows another embodiment where the coating 60 is thin but does not coat the entire circumference oftubular body 12. Thicknesses in the range of about 0.001 to about 0.0035 inches are preferred. In both of the embodiments shown in FIGS. 4A and 4B, preferably, the coating 60 has a thickness of no greater than about 0.01 inches, and more preferably, the coating thickness is no greater than about 0.0035 inches. Thus, it has been discovered that sufficient lubricity can be achieved with a nonuniform or even intermittent, sporadic coating, while simultaneously maintaining a low profile. - To apply the polymeric coating60 to the
tubular body 12, the surface of thetubular body 12 is first cleaned. Preferable cleaning methods are by preparing a cleaning solvent blend using a 1:1 (by volume) mixture of acetone and isopropyl alcohol. Thetubular body 12 may be cleaned by wiping the body with a lint-free towel or cloth wetted by this solvent blend. After the solvent wipe, thetubular body 12 is heat cleaned in an oven for 15 minutes at 540° F. - The Teflon coating solution may be Xylan 1006/870 Black Teflon coating as obtained from Whitford Corporation. To achieve a thinner film thickness, the coating can be mixed with a thinner such as thinner #99B from Whitford Corporation. To mix the coating solution with the thinner, the coating solution is first mixed well in a container using a mechanical stirrer for about 5 to 10 minutes to remove residue and Teflon particles from the bottom of the container. About 80 parts by volume of the coating solution is mixed with about 20 parts by volume of the thinner with a mechanical stirrer until the blend is uniform to achieve 0.0035 inch thickness. This blend is filtered using a cone type coarser filter paper to remove lumps. After completing these steps, the coating solution is ready to spray.
- The coating is produced on the tubular body by a spray gun, preferably with an agitating pressure pot, although a spray gun without an agitating pressure pot may be used. The spraying process of the present invention preferably produces a nonuniform Teflon coating 360 degrees around the tubular body and extending continuously along the length of the
tubular body 12. When applying the coating with the spray gun, rather than pulling the trigger all the way and holding it continuously, the trigger can be selectively depressed and released, or depressed with various degrees of pressure, as the gun passes from left to right over a portion of the tubular body. This process is repeated as the tubular body is rotated and a coating is applied 360 degrees around the tubular body. Coating on the tubular body by the spray gun can also be adjusted by controlling the flow rate of the spray exiting the gun. Moreover, the motion of the gun over the body allows control of the thickness and uniformity of the coating. These factors allow the coating 60 to be a thin, nonuniform coating covering substantially all of the tubular body, as shown in FIG. 4A. - Alternatively, the profile of the catheter can be reduced even further by spraying less than 360 degrees around the
tubular body 12, as shown in FIG. 4B. The nonuniformity of the coating, thus, results from thetubular body 12 having portions that are coated with the polymer and other portions having no coating at all. The degree of nonuniformity depends on how the trigger of the spray gun is selectively activated and deactivated. Other methods to produce nonuniformity on thetubular body 12, such as masking portions oftubular body 12, may also be used. Moreover, the nonuniformity may result from the coating not being sprayed continuously over the circumference and/or length of the body. - After spraying, the coating should be flashed off to avoid any blistering. The coated tubular bodies are flashed off in an oven at 200° F. for 15 minutes. Then, the tubular body is cured. When a NiTi material is used for the tubular body, a curing temperature of about 540° F. is used in order to maintain the heat treated superelastic properties of NiTi. The curing step takes about one-half hour. After allowing the coated tubular bodies to cool, parts of the tubular body may be stripped to remove the coating from undesired areas. For instance, at the location of the
proximal marker 62 shown in FIG. 1, no coating is desired. Suitable means for stripping include an abrasive and a razor blade, as well as other stripping means known to those skilled in the art. - In another aspect of the present invention, a
tubular marker 52, as shown in FIG. 2, is located within an adhesive taper 48 adjacent theballoon 22. Although themarker 52 is shown in the form of a tube, it will be appreciated by those skilled in the art that markers of other shapes may be used as well. To place themarker 52 within the taper 48, the marker is first slid over the coil 40 andcore wire 38 and over the distal tip of thetubular body 12 past theinflation notch 36 so that it is out of the way for balloon bonding. Adhesive stops 32 and 34 and theballoon 22 are then mounted to thetubular body 12 using adhesives or other means known to those skilled in the art. One preferred method for mounting the adhesive stops and balloon to the tubular body is described in the above-referenced application BALLOON CATHETER AND METHOD OF MANUFACTURE (Attorney Docket PERCUS.010CP1), application Ser. No. ______, filed on the same day as the present application. - After balloon bonding, the
marker 52 is slid towards theballoon 22 such that it is between about 0.5 and 3 mm from the proximal end of the balloon. More preferably, themarker 52 is located within about 1.0 mm from theproximal end 24 of theballoon 22. In the preferred embodiment shown in FIG. 2, themarker 52 is located about 0.75 mm from the balloon. The gap between theballoon 22 and themarker 52 is filled with an adhesive material taper 48. Preferably, a cyanoacrylate adhesive such as LOCTITE 4011 is used. However, as will be appreciated by those of skill in the art, other adhesives may be used. The taper 48 also extends from theproximal end 64 of the marker to point 66 on thetubular body 12, as well as from theproximal end 24 ofballoon 22 toproximal end 64 ofmarker 52. - Because the marker is placed within the adhesive taper48 of the
balloon 22, the marker can be made larger and closer to the balloon, thereby increasing visibility without obstructing advancement of an aspiration catheter or the like when thetubular body 12 is used as a guidewire. Further details regarding an aspiration catheter are disclosed in assignee's co-pending application entitled ASPIRATION CATHETER, application Ser. No. 08/813,308, filed Mar. 6, 1997, the entirety of which is hereby incorporated by reference. The marker preferably has an outer diameter of at least about 0.02 inches. More preferably, themarker 52 has an inner diameter of about 0.017 inches and an outer diameter of about 0.024 inches. The proximal cyanoacrylate balloon taper 48 is preferably about 4 mm long, extending frompoint 24 on theballoon 22 to point 66 on the tubular body. The marker taper, extending frompoint 24 to distal point 68 onmarker 52, is preferably about 0.75 mm long. - It will be appreciated that certain variations of the shaft of the present invention may suggest themselves to those skilled in the art. The foregoing detailed description is to be clearly understood as given by way of illustration, the spirit and scope of this invention being limited solely by the appended claims.
Claims (40)
1. A catheter, comprising:
a tubular body having proximal and distal sections, the tubular body having a lumen extending therethrough;
an expandable member with an interior volume mounted on the distal section of the tubular body, the expandable member having proximal and distal ends;
a notch formed by electric discharge machining in the tubular body for providing fluid communication between the lumen and the interior volume of the expandable member;
a nonuniform polymer coating formed on at least a portion of the tubular body to provide a substantially frictionless surface;
a marker mounted on the distal section of the tubular body adjacent the proximal end of the expandable member; and
a taper formed from the proximal end of the expandable member and covering the distal marker.
2. A catheter, comprising:
a tubular body having proximal and distal sections, the tubular body having a lumen extending therethrough; and
a notch formed by electric discharge machining in the tubular body.
3. The catheter of , further comprising an expandable member with an interior volume mounted on the distal section of the tubular body, wherein the notch provides fluid communication between the lumen and the interior volume of the expandable member.
claim 2
4. The catheter of , wherein the notch has a length of about 1.5 mm and a width of about 0.003 inches.
claim 3
5. A notch for a catheter body formed by electric discharge machining.
6. A method of manufacturing a notch in a catheter body, comprising the step of electric discharge machining at least a portion of the catheter body.
7. A catheter, comprising:
a tubular body having proximal and distal sections, the tubular body having a lumen extending therethrough; and
a notch formed by mechanical grinding of the tubular body.
8. The catheter of , further comprising an expandable member with an interior volume mounted on the distal section of the tubular body, wherein the notch provides fluid communication between the lumen and the interior volume of the expandable member.
claim 7
9. The catheter of , wherein the notch has a length of about 1.5 mm and a width of about 0.003 inches.
claim 8
10. A notch for a catheter body formed by mechanical grinding.
11. A method of manufacturing a notch in a catheter body comprising the step of mechanically grinding at least a portion of the catheter body.
12. A catheter, comprising:
an elongate shaft;
a nonuniform polymer coating formed onto at least a portion of the shaft to provide a substantially frictionless surface.
13. The catheter of , wherein the nonuniform polymer coating is produced by sputter coating.
claim 12
14. The catheter of , wherein the nonuniform coating is produced by selectively spraying a polymer coating onto the shaft.
claim 12
15. The catheter of , wherein the elongate shaft is substantially cylindrical.
claim 12
16. The catheter of , wherein the nonuniform coating formed onto at least a portion of the shaft provides a coating substantially 360 degrees around the shaft.
claim 13
17. The catheter of , wherein the nonuniform coating formed onto at least a portion of the shaft provides a coating less than 360 degrees around the shaft.
claim 13
18. The catheter of , wherein the nonuniform coating is formed by coating the shaft with a polymer coating of varying thickness.
claim 12
19. The catheter of , wherein the nonuniform coating is formed by providing coated and uncoated portions on the shaft.
claim 12
20. The catheter of , wherein the polymer coating is made of a polytetrafluoroethylene.
claim 12
21. A method of lubricating a catheter shaft, comprising the step of coating the catheter shaft with a polymeric material to form a nonuniform coating on the catheter shaft.
22. The method of , wherein the step of coating comprises selectively spraying the polymeric material onto the shaft.
claim 21
23. The method of , wherein the step of coating comprises sputter coating the polymeric material onto the shaft.
claim 21
24. The method of , wherein the step of coating produces a nonuniform coating of varying degrees of thickness.
claim 21
25. The method of , wherein the step of coating produces a nonuniform coating on the shaft wherein coated and uncoated portions are provided on the shaft.
claim 21
26. A method of reducing the profile of a medical catheter, comprising the step of producing a nonuniform coating on the catheter.
27. The catheter of , wherein the nonuniform coating is formed by coating the catheter with a polymer coating of varying thickness.
claim 26
28. The catheter of , wherein the nonuniform coating is formed by providing coated and uncoated portions on the catheter.
claim 26
29. The catheter of , wherein the coating is made of a polytetrafluoroethylene.
claim 26
30. A catheter, comprising:
an elongate body having proximal and distal sections;
an expandable member mounted on the distal section of the tubular body, the expandable member having proximal and distal ends;
a marker mounted on the distal section of the elongate body adjacent the proximal end of the expandable member; and
a taper formed from the proximal end of the expandable member in a proximal direction to the elongate body and covering the distal marker.
31. The catheter of , wherein the marker is a tube.
claim 30
32. The catheter of , wherein the marker is radiopaque.
claim 30
33. The catheter of , wherein the marker is located within about 3 mm of the proximal end of the expandable member.
claim 30
34. The catheter of , wherein the taper is formed from a cyanoacrylate adhesive.
claim 30
35. The catheter of , wherein the marker has an outer diameter of at least about 0.020 inches.
claim 30
36. A method of manufacturing a balloon catheter having a radiopaque marker, comprising the steps of:
providing an elongate body with proximal and distal ends;
providing a balloon having proximal and distal ends;
providing a radiopaque marker;
mounting the balloon over the elongate body so that the balloon is in an appropriate position for balloon bonding;
mounting the marker over the elongate body at a position adjacent the proximal end of the balloon forming a gap between the marker and the balloon; and
forming a taper from the proximal end of the balloon to the elongate body toward the proximal end of the elongate body, the taper filling the gap between the balloon and the marker and covering the marker.
37. The method of , wherein the taper is a cyanoacrylate adhesive.
claim 36
38. The method of , wherein the marker is positioned within about 3 mm of the proximal end of the balloon.
claim 36
39. A catheter, comprising:
an elongate shaft;
a radiopaque marker for locating a desired point on the shaft; and
an adhesive taper covering the marker.
40. A method of locating a desired point on a catheter when inserted inside a human body, comprising the steps of:
providing an elongate catheter shaft;
providing a radiopaque marker located at the desired point on the catheter shaft; and
forming a taper covering the marker.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
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US09/382,610 US20010016705A1 (en) | 1998-02-19 | 1999-08-25 | Shaft for medical catheters |
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Application Number | Priority Date | Filing Date | Title |
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US09/026,105 US6228072B1 (en) | 1998-02-19 | 1998-02-19 | Shaft for medical catheters |
US09/382,610 US20010016705A1 (en) | 1998-02-19 | 1999-08-25 | Shaft for medical catheters |
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US09/383,103 Expired - Fee Related US6273878B1 (en) | 1998-02-19 | 1999-08-25 | Shaft for medical catheters |
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-
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- 1998-02-19 US US09/026,105 patent/US6228072B1/en not_active Expired - Fee Related
-
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- 1999-02-19 AU AU26874/99A patent/AU2687499A/en not_active Abandoned
- 1999-02-19 WO PCT/US1999/003591 patent/WO1999042164A1/en not_active Application Discontinuation
- 1999-02-19 EP EP99907145A patent/EP1056504A1/en not_active Withdrawn
- 1999-08-25 US US09/382,610 patent/US20010016705A1/en not_active Abandoned
- 1999-08-25 US US09/383,103 patent/US6273878B1/en not_active Expired - Fee Related
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US8801683B2 (en) | 2002-08-21 | 2014-08-12 | Hollister Incorporated | Bowel management system |
US8323255B2 (en) | 2002-08-21 | 2012-12-04 | Hollister Incorporated | Bowel management system |
US20090005755A1 (en) * | 2002-11-22 | 2009-01-01 | Keith Peter T | Guide wire control catheter for crossing occlusions and related methods of use |
US20040225318A1 (en) * | 2003-05-05 | 2004-11-11 | Tracee Eidenschink | Balloon catheter and method of making same |
US7306616B2 (en) | 2003-05-05 | 2007-12-11 | Boston Scientific Scimed, Inc. | Balloon catheter and method of making same |
US7763012B2 (en) | 2003-09-02 | 2010-07-27 | St. Jude Medical, Cardiology Division, Inc. | Devices and methods for crossing a chronic total occlusion |
US20050049574A1 (en) * | 2003-09-02 | 2005-03-03 | Velocimed Dmc, Inc. | Devices and methods for crossing a chronic total occlusion |
EP1607038A3 (en) * | 2004-06-14 | 2006-01-25 | Fujinon Corporation | Endoscope apparatus |
EP1964508A3 (en) * | 2004-06-14 | 2012-05-30 | FUJIFILM Corporation | Endoscope apparatus |
US20050277809A1 (en) * | 2004-06-14 | 2005-12-15 | Fujinon Corporation | Endoscope apparatus |
US7654264B2 (en) | 2006-07-18 | 2010-02-02 | Nellcor Puritan Bennett Llc | Medical tube including an inflatable cuff having a notched collar |
US8096299B2 (en) | 2006-07-18 | 2012-01-17 | Nellcor Puritan Bennett Llc | Medical tube including an inflatable cuff having a notched collar |
US20130184683A1 (en) * | 2011-07-25 | 2013-07-18 | Mina W.B. Chow | Devices and methods for transnasal dilation and irrigation of the sinuses |
US9095646B2 (en) * | 2011-07-25 | 2015-08-04 | Acclarent, Inc. | Devices and methods for transnasal dilation and irrigation of the sinuses |
US20130184568A1 (en) * | 2011-07-28 | 2013-07-18 | Ketan P. Muni | Device and method for dilating an airway stenosis |
US9095364B2 (en) * | 2011-07-28 | 2015-08-04 | Acclarent, Inc. | Device and method for dilating an airway stenosis |
Also Published As
Publication number | Publication date |
---|---|
EP1056504A1 (en) | 2000-12-06 |
AU2687499A (en) | 1999-09-06 |
WO1999042164A1 (en) | 1999-08-26 |
US6228072B1 (en) | 2001-05-08 |
US6273878B1 (en) | 2001-08-14 |
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Legal Events
Date | Code | Title | Description |
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STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |