US20030009151A1 - Biaxially oriented multilayer polymer tube for medical devices - Google Patents
Biaxially oriented multilayer polymer tube for medical devices Download PDFInfo
- Publication number
- US20030009151A1 US20030009151A1 US09/898,717 US89871701A US2003009151A1 US 20030009151 A1 US20030009151 A1 US 20030009151A1 US 89871701 A US89871701 A US 89871701A US 2003009151 A1 US2003009151 A1 US 2003009151A1
- Authority
- US
- United States
- Prior art keywords
- tubular
- layer
- medical device
- polymer member
- rotating
- 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.)
- Abandoned
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
- A61M25/00—Catheters; Hollow probes
- A61M25/0009—Making of catheters or other medical or surgical tubes
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B29—WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE IN GENERAL
- B29C—SHAPING OR JOINING OF PLASTICS; SHAPING OF MATERIAL IN A PLASTIC STATE, NOT OTHERWISE PROVIDED FOR; AFTER-TREATMENT OF THE SHAPED PRODUCTS, e.g. REPAIRING
- B29C48/00—Extrusion moulding, i.e. expressing the moulding material through a die or nozzle which imparts the desired form; Apparatus therefor
- B29C48/03—Extrusion moulding, i.e. expressing the moulding material through a die or nozzle which imparts the desired form; Apparatus therefor characterised by the shape of the extruded material at extrusion
- B29C48/09—Articles with cross-sections having partially or fully enclosed cavities, e.g. pipes or channels
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B29—WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE IN GENERAL
- B29C—SHAPING OR JOINING OF PLASTICS; SHAPING OF MATERIAL IN A PLASTIC STATE, NOT OTHERWISE PROVIDED FOR; AFTER-TREATMENT OF THE SHAPED PRODUCTS, e.g. REPAIRING
- B29C48/00—Extrusion moulding, i.e. expressing the moulding material through a die or nozzle which imparts the desired form; Apparatus therefor
- B29C48/16—Articles comprising two or more components, e.g. co-extruded layers
- B29C48/18—Articles comprising two or more components, e.g. co-extruded layers the components being layers
- B29C48/21—Articles comprising two or more components, e.g. co-extruded layers the components being layers the layers being joined at their surfaces
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B29—WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE IN GENERAL
- B29C—SHAPING OR JOINING OF PLASTICS; SHAPING OF MATERIAL IN A PLASTIC STATE, NOT OTHERWISE PROVIDED FOR; AFTER-TREATMENT OF THE SHAPED PRODUCTS, e.g. REPAIRING
- B29C48/00—Extrusion moulding, i.e. expressing the moulding material through a die or nozzle which imparts the desired form; Apparatus therefor
- B29C48/25—Component parts, details or accessories; Auxiliary operations
- B29C48/30—Extrusion nozzles or dies
- B29C48/32—Extrusion nozzles or dies with annular openings, e.g. for forming tubular articles
- B29C48/33—Extrusion nozzles or dies with annular openings, e.g. for forming tubular articles with parts rotatable relative to each other
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B29—WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE IN GENERAL
- B29C—SHAPING OR JOINING OF PLASTICS; SHAPING OF MATERIAL IN A PLASTIC STATE, NOT OTHERWISE PROVIDED FOR; AFTER-TREATMENT OF THE SHAPED PRODUCTS, e.g. REPAIRING
- B29C48/00—Extrusion moulding, i.e. expressing the moulding material through a die or nozzle which imparts the desired form; Apparatus therefor
- B29C48/25—Component parts, details or accessories; Auxiliary operations
- B29C48/30—Extrusion nozzles or dies
- B29C48/32—Extrusion nozzles or dies with annular openings, e.g. for forming tubular articles
- B29C48/335—Multiple annular extrusion nozzles in coaxial arrangement, e.g. for making multi-layered tubular articles
- B29C48/336—Multiple annular extrusion nozzles in coaxial arrangement, e.g. for making multi-layered tubular articles the components merging one by one down streams in the die
-
- 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
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B29—WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE IN GENERAL
- B29L—INDEXING SCHEME ASSOCIATED WITH SUBCLASS B29C, RELATING TO PARTICULAR ARTICLES
- B29L2031/00—Other particular articles
- B29L2031/753—Medical equipment; Accessories therefor
- B29L2031/7542—Catheters
Definitions
- the present invention generally relates to extruded polymer tubular members for medical devices. More specifically, the present invention relates to extruded polymer tubular members for medical devices having helical orientation.
- intravascular catheters and guide wires commonly utilize an extruded polymeric tube as a shaft component. Because intravascular catheters and guide wires must exhibit good torqueability, trackability and pushability, it is desirable that the extruded polymeric shaft component have good torque transmission, flexibility and column strength. These attributes are commonly incorporated into intravascular catheters by utilizing a composite shaft construction. Alternatively, the polymer material which forms the extruded polymeric shaft component may be oriented to enhance the mechanical characteristics thereof.
- U.S. Pat. No. 5,951,494 to Wang et al. discloses a variety of medical instruments, such as guide wires and catheters, formed at least in part of elongated polymer members having helical orientation.
- the helical orientation is established by post-processing an extruded elongate polymer member with tension, heat and twisting. Wang et al. theorize that the tension, heat and twisting process results in a polymer member that has helical orientation on the molecular level.
- Such molecular helical orientation enhances torque transmission of the elongate polymer member, which is important for some types of intravascular medical devices to navigate through tortuous vascular pathways.
- U.S. Pat. No. 5,059,375 to Lindsay discloses an extrusion process for producing flexible kink resistant tubing having one or more spirally-reinforced sections.
- the extruder includes a rotatable member having an extrusion passageway for spirally extruding a thermoplastic filament into a base thermoplastic material to form a tube.
- the rotatable member is rotated to form the reinforcement filament in a spiral or helical pattern in the wall of the tubing.
- U.S. Pat. No. 5,639,409 to Van Muiden discloses an extrusion process for manufacturing a tube-like extrusion profile by conveying a number of divided streams of material of at least two different compositions through a rotating molding nozzle. The streams of material flow together in the rotating molding nozzle to form at least two helically shaped bands of material. After allowing the combined streams of material to cool off, an extrusion profile comprising a plurality of bands of material extending in a helical pattern is formed.
- U.S. Pat. No. 5,248,305 to Zdrahala discloses a method of manufacturing extruded catheters and other flexible plastic tubing with improved rotational and/or longitudinal stiffness.
- the tubing comprises a polymer material including liquid crystal polymer (LCP) fibrils extruded through a tube extrusion die while rotating the inner and outer die walls to provide circumferential shear to the extruded tube. Rotation of the inner and outer die walls orients the LCP in a helical manner to provide improved properties, including greater rotational stiffness.
- LCP liquid crystal polymer
- the present invention provides a tubular extruded member particularly suitable for use in medical devices such as intravascular catheters and guide wires, wherein the extruded tubular member includes multiple layers having biaxial helical orientation in different directions.
- a counter-rotation extrusion process may be used to orient the layers in different helical directions.
- the counter-rotation extrusion process provides orientation in two different circumferential directions in addition to a longitudinal direction.
- different layers of the tubular member may be tailored to have the desired mechanical properties.
- the outer layer may be formed of a relatively rigid material.
- the inner layer may be formed of a relatively soft and flexible material.
- the inner layer may incorporate a relatively hard and thin material.
- the outer layer may be formed of a relatively soft and durable material.
- the multi-layer tube incorporates biaxial helical orientation in different directions to enhance the mechanical properties thereof.
- FIG. 1 is a plan view of a multi-layered extruded tube in accordance with an embodiment of the present invention
- FIG. 2 is a cross-sectional view taken along line 2 - 2 in FIG. 1;
- FIG. 3 is a plan view of an intravascular balloon catheter incorporating the tubular member illustrated in FIG. 1;
- FIG. 4 is a schematic illustration of an extrusion process for manufacturing the tubular member illustrated in FIG. 1;
- FIG. 5 is a schematic illustration of an alternative manufacturing process for manufacturing the tubular member illustrated in FIG. 1.
- FIG. 1 illustrates a tubular polymer extruded member 10 in accordance with the present invention.
- Extruded tubular polymer member 10 includes a plurality of coaxial tubular layers 12 / 14 and a lumen 16 as best seen in FIG. 2, which is a cross-sectional view taken along line 2 - 2 in FIG. 1.
- the tubular member 10 is shown to include two layers, namely an inner layer 12 and an outer layer 14 . It is to be understood, however, that the tubular member 10 may incorporate virtually any number of concentric tubular layers, depending on the desired characteristics of the tubular member 10 .
- the tubular member 10 has orientation in two different circumferential directions as indicated by reference lines 22 and 24 .
- Reference line 22 illustrates the helical orientation of the inner tubular layer 12 and reference line 24 illustrates the helical orientation of outer layer 14 .
- Reference line 26 shown in FIG. 2 illustrates the different rotational directions of the biaxial helical orientation. In this particular example, reference line 26 illustrates clockwise rotational orientation in the outer layer 14 and counter-clockwise rotational orientation in the inner layer 12 . It is to be understood that the rotational orientation may be reversed. In particular, the outer layer 14 may have counter-clockwise rotational orientation and the inner layer 12 may have clockwise rotational orientation.
- the outer layer 14 may include a helically oriented relatively rigid material to increase torsional rigidity.
- the inner layer 12 may include a helically oriented relatively rigid material to increase hoop strength (i.e., burst strength).
- the inner layer 12 may include a helically oriented relatively flexible material to increase kink resistance.
- the outer layer 14 may include a helically oriented relatively durable material to increase puncture resistance.
- FIG. 3 illustrates an intravascular balloon catheter 30 , which is substantially conventional with the exception of incorporating one or more of the several embodiments of the tubular member 10 described with reference to FIG. 1.
- the intravascular balloon catheter 30 includes an elongate shaft 32 having a proximal end and a distal end.
- a conventional manifold 34 is connected to the proximal end of the elongate shaft 32 .
- An inflatable balloon 36 is connected to the distal end of the elongate shaft 32 .
- the elongate shaft 32 may be formed at least in part of the multi-layer tube 10 described with reference to FIGS. 1 and 2.
- the balloon 36 may be formed at least in part from a blow-molded multi-layer tube 10 .
- the inner layer 12 may be formed of a relatively hard and rigid polymeric material. Concentrating the relatively hard and rigid polymeric material in the inner layer 12 increases hoop strength (i.e., burst strength) and improves kink resistance of the tubular member 10 .
- Providing a catheter 30 having a shaft 32 and a balloon 36 that is able to withstand high inflation pressures is advantageous for certain clinical applications requiring high inflation pressure.
- Providing a catheter 30 having a shaft 32 that is kink resistant is advantageous because damage due to handling and/or navigation through tortuous vasculature is mitigated.
- the inner layer 12 may be formed of a relatively soft and flexible polymeric material. Concentrating the relatively soft and flexible polymeric material in the inner layer 12 improves kink resistance of the tubular member 10 if the outer layer 14 is formed of a material susceptible to kinking. As mentioned above, providing a catheter 30 having a shaft 32 that is kink resistant is advantageous because damage due to handling and/or navigation through tortuous vasculature is mitigated.
- the outer layer 14 may comprise a relatively hard and rigid polymeric material. Concentrating the relatively hard and rigid polymeric material in the outer layer 14 increases rotational stiffness and column strength of the tubular member 10 .
- Providing an intravascular guide wire having a shaft with increased rotational stiffness is advantageous in clinical applications requiring 1:1 torque response for precise steering, particularly in tortuous vasculature.
- providing an intravascular guide wire and/or catheter 30 having a shaft 32 with increased column strength is advantageous in clinical applications requiring substantial longitudinal force transmission over long distances as is usually required to cross tight vascular restrictions.
- the outer layer 14 may be formed of a relatively soft and flexible polymeric material. Concentrating a relatively soft and flexible polymeric material in the outer layer 14 improves the durability of the tubular member 10 . Providing a catheter 30 having a balloon 36 with increased durability mitigates the likelihood of balloon burst due to puncture from a calcified vascular deposit or from a stent.
- the multi-layer tube 10 When utilized to form a portion of the elongate shaft 32 , the multi-layer tube 10 may have a wall thickness ranging from approximately 0.002 inches to 0.010 inches, and a length ranging from 10 cm to 150 cm. When utilized to form the balloon 36 , the multi-layer tube 10 may have a wall thickness (post blow-molding) ranging from 0.0005 inches to 0.002 inches, and a length ranging from 1 cm to 10 cm. These dimensions are provided by way of example, not limitation.
- each layer 12 / 14 may be modified to balance the respective properties of the elongate shaft 32 or balloon 36 .
- the thickness of the inner and outer layers of 12 / 14 may be modified and/or the materials selected for the inner and outer layers 12 / 14 may be modified.
- suitable rigid polymers include polyurethane (isoplastic), aromatic polyamide, polyamide, PET, PEN, LCP, polycarbonate, aromatic polyester, etc.
- suitable soft and flexible polymers include polyurethane elastamers, polyether block amides (PEBA), Pellethane, Hytrel, Arnitel, Estane, Pebax, Grilamid, Vestamid, Riteflex, etc.
- a specific example of a hard-soft multiple-layer combination is one layer formed of a polyamide (e.g., nylon or PEBA) and another layer formed of polyethylene with a tie-layer of polyethylene copolymer disposed therebetween.
- a hard-soft multiple-layer combination is one layer formed of aromatic nylon and the other layer formed of nylon 12 .
- the inner and/or outer layers 12 / 14 may also comprise a reinforced polymer structure such as a polymer layer including continuous liquid crystal polymer fibers (LCP) dispersed in a non-LCP thermal plastic polymer matrix.
- LCP liquid crystal polymer fibers
- the LCP content of the LCP containing layer may be greater than 0.1% by weight and less than 90% by weight.
- the LCP containing layer may comprise 0.05% to 50% by weight of the combined layers.
- Extrusion system 100 includes one or more extruders 50 A/ 50 B coupled to an extrusion head 40 as schematically illustrated by extrusion lines 60 .
- Each extruder 50 A/ 50 B includes a hopper 52 , a heated barrel 56 , an extrusion screw 58 , and a control system 54 .
- the control system 54 of each extruder 50 A/ 50 B is operably coupled as indicated by dashed line 51 to facilitate co-extrusion.
- Extrusion head 40 includes an outer die portion 42 having a fixed portion 42 F and a rotatable portion 42 R. Extrusion head 40 further includes a rotatable pin 44 rotatably disposed in the outer die portions 42 F and 42 R.
- Molten polymer enters the extrusion head 40 at inlets 48 A and 48 B. The molten polymer entering inlet 48 A forms the inner layer 12 and the molten polymer entering inlet 48 B forms the outer layer 14 of the multi-layer extrusion 10 .
- the molten polymer flows through the extrusion passages as indicated by the small arrows.
- the molten polymer exits the extrusion head 40 through outlet 46 .
- the molten polymer Upon exiting the extrusion head 40 through outlet 46 , the molten polymer begins to solidify to form the multi-layer tube 10 which may be subsequently cut to length or taken up by spool 80 .
- the rotatable pin 44 is coupled to a rotational drive 70 A which rotates in the direction indicated by arrow 76 A.
- the rotational drive 70 A may comprise, for example, a motor 72 coupled to the rotational pin 44 by a chain or belt 74 .
- the rotational outer die 42 R is connected to rotational drive 70 B which rotates in the direction indicated by arrow 76 B. Note that the direction of rotation of drive 70 A is different than the rotational direction of drive 70 B, thereby rotating the pin 44 in a different direction than the outer die 42 R.
- the rotatable outer die imparts helical orientation to the outer layer 14 of the tubular member 10 .
- the rotating pin 44 imparts helical orientation to the inner layer 12 of the tubular member 10 . Because the pin 44 is rotated in the opposite direction of rotatable outer die 42 R, the helical orientation imparted to the outer layer 14 is in the opposite direction of the helical orientation imparted to the inner layer 12 .
- an air passage may extend through the pin 44 , which may be used to pump air into the tubular member 10 as it solidifies to help maintain the lumen 16 therein.
- the pin 44 may be used to pump air into the tubular member 10 as it solidifies to help maintain the lumen 16 therein.
- the biaxial helical orientation imparted to the inner and outer layers 12 / 14 is locked into the tubular member 10 .
- FIG. 5 illustrates an alternative extrusion system 200 for manufacturing the multi-layer tubular member 10 .
- the extrusion system 200 is similar to the extrusion systems described in co-pending patent application ______ filed on even date herwith, entitled MEDICAL DEVICE WITH EXTRUDED MEMBER HAVING HELICAL ORIENTATION, the entire disclosure of which is hereby incorporated by reference.
- Extrusion system 200 includes two or more extruders 50 A/ 50 B coupled to extrusion head 40 substantially as described previously. However, in this embodiment, the pin 44 remains stationary and is hollow to serve as a guide for mandrel 90 .
- Molten polymer enters the extrusion head 40 at inlets 48 A/ 48 B and flows through the extrusion passages as indicated by the small arrows. The molten polymer exits the extrusion head 40 through outlet 46 .
- the molten polymer Upon exiting the extrusion head 40 through outlet 46 , the molten polymer begins to solidify thereby creating a semi-molten polymer state. In a semi-molten state, the polymer typically has a temperature below the melting point but at or above the glass transition point.
- the multi-layer tubular member 10 is rotated by rotational drive 70 C in a direction indicated by arrow 76 C.
- the support mandrel 90 is also rotated by a rotational drive 70 A in a direction indicated by arrow 76 A.
- the support mandrel 90 and the multi-layered tubular member 10 are rotated in the same direction, while the rotational outer die 42 R is rotated in the opposite direction by rotational drive 70 B as indicated by arrow 76 B.
- a molecular helical orientation is imparted to both the inner layer 12 and the outer layer 14 .
- the crystalline regions of the polymer are helically oriented by rotation and subsequently allowed to cool thereby locking in the biaxial helical orientation on the molecular level.
- Helical orientation is also imparted to the outer tubular layer 14 in the opposite direction by virtue of the rotating outer die 42 R.
- the multi-layer tubular member 10 may be cut into discrete lengths immediately after extrusion or spooled onto take-up spool 80 A.
- the multi-layer tubular member 10 is taken-up by spool 80 A, the multi-layer tubular member 10 and the spool 80 A may be rotated simultaneously.
- the support mandrel 90 is provided on a spool 80 B, the spool 80 B and the support mandrel 90 may be rotated simultaneously.
- a further alternative extrusion system for manufacturing the multi-layer tubular member 10 is partially disclosed in U.S. Pat. No. 5,622,665 to Wang, the entire disclosure of which is hereby incorporated by reference.
- Wang '665 discloses a method for making differential stiffness tubing for medical products, such as catheters. The method produces a tubing that has a stiff section and a flexible section joined by a relatively short transition section in which the materials of the stiff and flexible sections are wedged into each other in a smooth gradual manner to produce an inseparable bond between the materials without abrupt joints.
- the method also employs a resin modulating system that minimizes the length of the transition section by minimizing the volumes in all flow channels of the co-extrusion head used to produce the tubing.
- Wang '665 further discloses a system for co-extruding differential stiffness tubing.
- the system includes a co-extrusion head into which extruders feed the different resins, such as a soft resin and a stiff resin, that will be used to form the finished tubing.
- a modulating device regulates the flow of the resins from each of the extruders into the co-extrusion head, while another modulator may be used to bleed resin “A” from the head to relieve residual pressure.
- the modulators are actuated periodically and in synchronized fashion to abruptly stop or change the resin flow to the head.
- the interface between the stiff resin and soft resin is naturally sheared and elongated when flowing through the flow channels of the head.
- these abrupt changes or stoppages by the modulators result in a very gradual change of stiff layer thickness in the tubing, creating the gradual stiffness change of the tubing.
- the tubing After discharge from the head, the tubing is cooled by passage through a water tank to form the tubing.
- a rotational drive may be coupled to the pin in the co-extrusion head of Wang '665, and a rotational drive may be coupled to the die of Wang '665, with the necessary modifications made to the co-extrusion head to permit such rotation.
- the rotational drives may comprise, for example, a motor coupled to the pin and die by a chain or belt. The direction of rotation of the pin drive is different than the rotational direction of the die drive, thereby rotating the pin in a different direction than the die.
- the rotatable die imparts helical orientation to the outer layer 14 of the tubular member 10 and the rotatable pin imparts helical orientation to the inner layer 12 in the opposite direction.
- an air passage may extend through the pin 44 , which may be used to pump air into the tubular member 10 as it solidifies to help maintain the lumen 16 therein.
- the biaxial helical orientation imparted to the inner and outer layers 12 / 14 is locked into the tubular member 10 .
Landscapes
- Engineering & Computer Science (AREA)
- Mechanical Engineering (AREA)
- Health & Medical Sciences (AREA)
- Manufacturing & Machinery (AREA)
- Life Sciences & Earth Sciences (AREA)
- Biomedical Technology (AREA)
- Pulmonology (AREA)
- Anesthesiology (AREA)
- Biophysics (AREA)
- Heart & Thoracic Surgery (AREA)
- Hematology (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Materials For Medical Uses (AREA)
- Extrusion Moulding Of Plastics Or The Like (AREA)
- Media Introduction/Drainage Providing Device (AREA)
Abstract
A tubular extruded member particularly suitable for use in medical devices such as intravascular catheters and guide wires, wherein the extruded tubular member includes multiple layers having biaxial helical orientation in different directions. A counter-rotation extrusion process may be used to orient the layers in different biaxial helical directions. The counter-rotation extrusion process provides orientation in two different circumferential directions in addition to a longitudinal direction. By combining the dual direction or biaxial helical orientation with multiple layers, different layers of the tubular member may be tailored to have the desired mechanical properties.
Description
- This application is related to co-pending patent application Ser. No. ______ filed on even date herewith, entitled MEDICAL DEVICE WITH EXTRUDED MEMBER HAVING HELICAL ORIENTATION (attorney docket 1001.1468101), the entire disclosure of which is hereby incorporated by reference.
- The present invention generally relates to extruded polymer tubular members for medical devices. More specifically, the present invention relates to extruded polymer tubular members for medical devices having helical orientation.
- A wide variety of medical devices utilized extruded polymeric members. For example, intravascular catheters and guide wires commonly utilize an extruded polymeric tube as a shaft component. Because intravascular catheters and guide wires must exhibit good torqueability, trackability and pushability, it is desirable that the extruded polymeric shaft component have good torque transmission, flexibility and column strength. These attributes are commonly incorporated into intravascular catheters by utilizing a composite shaft construction. Alternatively, the polymer material which forms the extruded polymeric shaft component may be oriented to enhance the mechanical characteristics thereof.
- For example, U.S. Pat. No. 5,951,494 to Wang et al. discloses a variety of medical instruments, such as guide wires and catheters, formed at least in part of elongated polymer members having helical orientation. The helical orientation is established by post-processing an extruded elongate polymer member with tension, heat and twisting. Wang et al. theorize that the tension, heat and twisting process results in a polymer member that has helical orientation on the molecular level. Such molecular helical orientation enhances torque transmission of the elongate polymer member, which is important for some types of intravascular medical devices to navigate through tortuous vascular pathways.
- U.S. Pat. No. 5,059,375 to Lindsay discloses an extrusion process for producing flexible kink resistant tubing having one or more spirally-reinforced sections. The extruder includes a rotatable member having an extrusion passageway for spirally extruding a thermoplastic filament into a base thermoplastic material to form a tube. The rotatable member is rotated to form the reinforcement filament in a spiral or helical pattern in the wall of the tubing.
- U.S. Pat. No. 5,639,409 to Van Muiden discloses an extrusion process for manufacturing a tube-like extrusion profile by conveying a number of divided streams of material of at least two different compositions through a rotating molding nozzle. The streams of material flow together in the rotating molding nozzle to form at least two helically shaped bands of material. After allowing the combined streams of material to cool off, an extrusion profile comprising a plurality of bands of material extending in a helical pattern is formed.
- U.S. Pat. No. 5,248,305 to Zdrahala discloses a method of manufacturing extruded catheters and other flexible plastic tubing with improved rotational and/or longitudinal stiffness. The tubing comprises a polymer material including liquid crystal polymer (LCP) fibrils extruded through a tube extrusion die while rotating the inner and outer die walls to provide circumferential shear to the extruded tube. Rotation of the inner and outer die walls orients the LCP in a helical manner to provide improved properties, including greater rotational stiffness.
- Although each of these prior art methods provide some degree of orientation which enhances the mechanical characteristics of extruded polymeric members, there is an ongoing need to further enhance the mechanical characteristics of medical devices such as intravascular catheters and guide wires to improve performance thereof.
- The present invention provides a tubular extruded member particularly suitable for use in medical devices such as intravascular catheters and guide wires, wherein the extruded tubular member includes multiple layers having biaxial helical orientation in different directions. A counter-rotation extrusion process may be used to orient the layers in different helical directions. The counter-rotation extrusion process provides orientation in two different circumferential directions in addition to a longitudinal direction. By combining the dual direction helical orientation with multiple layers, different layers of the tubular member may be tailored to have the desired mechanical properties. Thus, for example, to increase torque transmission of an intravascular guide wire, the outer layer may be formed of a relatively rigid material. To increase column strength and/or kink resistance of an intravascular catheter, the inner layer may be formed of a relatively soft and flexible material. To increase burst strength of an intravascular balloon, the inner layer may incorporate a relatively hard and thin material. To increase puncture resistance of an intravascular balloon, the outer layer may be formed of a relatively soft and durable material. In each instance, the multi-layer tube incorporates biaxial helical orientation in different directions to enhance the mechanical properties thereof.
- FIG. 1 is a plan view of a multi-layered extruded tube in accordance with an embodiment of the present invention;
- FIG. 2 is a cross-sectional view taken along line2-2 in FIG. 1;
- FIG. 3 is a plan view of an intravascular balloon catheter incorporating the tubular member illustrated in FIG. 1;
- FIG. 4 is a schematic illustration of an extrusion process for manufacturing the tubular member illustrated in FIG. 1; and
- FIG. 5 is a schematic illustration of an alternative manufacturing process for manufacturing the tubular member illustrated in FIG. 1.
- The following detailed description should be read with reference to the drawings in which similar elements in different drawings are numbered the same. The drawings, which are not necessarily to scale, depict illustrative embodiments and are not intended to limit the scope of the invention.
- Refer now to FIG. 1 which illustrates a tubular polymer extruded
member 10 in accordance with the present invention. Extrudedtubular polymer member 10 includes a plurality of coaxialtubular layers 12/14 and alumen 16 as best seen in FIG. 2, which is a cross-sectional view taken along line 2-2 in FIG. 1. For purposes of illustration only, thetubular member 10 is shown to include two layers, namely aninner layer 12 and anouter layer 14. It is to be understood, however, that thetubular member 10 may incorporate virtually any number of concentric tubular layers, depending on the desired characteristics of thetubular member 10. - The
tubular member 10 has orientation in two different circumferential directions as indicated byreference lines Reference line 22 illustrates the helical orientation of the innertubular layer 12 andreference line 24 illustrates the helical orientation ofouter layer 14.Reference line 26 shown in FIG. 2 illustrates the different rotational directions of the biaxial helical orientation. In this particular example,reference line 26 illustrates clockwise rotational orientation in theouter layer 14 and counter-clockwise rotational orientation in theinner layer 12. It is to be understood that the rotational orientation may be reversed. In particular, theouter layer 14 may have counter-clockwise rotational orientation and theinner layer 12 may have clockwise rotational orientation. - By combining the dual direction or biaxial helical orientation with
multiple layers 12/14, different layers of thetubular member 10 may be tailored to have the desired mechanical properties. For example, theouter layer 14 may include a helically oriented relatively rigid material to increase torsional rigidity. Alternatively, theinner layer 12 may include a helically oriented relatively rigid material to increase hoop strength (i.e., burst strength). As a further alternative, theinner layer 12 may include a helically oriented relatively flexible material to increase kink resistance. As yet a further alternative, theouter layer 14 may include a helically oriented relatively durable material to increase puncture resistance. These and other examples oftubular member 10 are particularly useful when incorporated into a medical device such ascatheter 30 described with reference to FIG. 3. - FIG. 3 illustrates an
intravascular balloon catheter 30, which is substantially conventional with the exception of incorporating one or more of the several embodiments of thetubular member 10 described with reference to FIG. 1. Theintravascular balloon catheter 30 includes anelongate shaft 32 having a proximal end and a distal end. Aconventional manifold 34 is connected to the proximal end of theelongate shaft 32. Aninflatable balloon 36 is connected to the distal end of theelongate shaft 32. Theelongate shaft 32 may be formed at least in part of themulti-layer tube 10 described with reference to FIGS. 1 and 2. In addition, theballoon 36 may be formed at least in part from a blow-moldedmulti-layer tube 10. - As mentioned previously, providing a
multi-layer tube 10 allows each of theindividual layers 12/14 to be tailored with the desired features. For example, theinner layer 12 may be formed of a relatively hard and rigid polymeric material. Concentrating the relatively hard and rigid polymeric material in theinner layer 12 increases hoop strength (i.e., burst strength) and improves kink resistance of thetubular member 10. Providing acatheter 30 having ashaft 32 and aballoon 36 that is able to withstand high inflation pressures is advantageous for certain clinical applications requiring high inflation pressure. Providing acatheter 30 having ashaft 32 that is kink resistant is advantageous because damage due to handling and/or navigation through tortuous vasculature is mitigated. - Alternatively, the
inner layer 12 may be formed of a relatively soft and flexible polymeric material. Concentrating the relatively soft and flexible polymeric material in theinner layer 12 improves kink resistance of thetubular member 10 if theouter layer 14 is formed of a material susceptible to kinking. As mentioned above, providing acatheter 30 having ashaft 32 that is kink resistant is advantageous because damage due to handling and/or navigation through tortuous vasculature is mitigated. - The
outer layer 14 may comprise a relatively hard and rigid polymeric material. Concentrating the relatively hard and rigid polymeric material in theouter layer 14 increases rotational stiffness and column strength of thetubular member 10. Providing an intravascular guide wire having a shaft with increased rotational stiffness is advantageous in clinical applications requiring 1:1 torque response for precise steering, particularly in tortuous vasculature. In addition, providing an intravascular guide wire and/orcatheter 30 having ashaft 32 with increased column strength is advantageous in clinical applications requiring substantial longitudinal force transmission over long distances as is usually required to cross tight vascular restrictions. - Alternatively, the
outer layer 14 may be formed of a relatively soft and flexible polymeric material. Concentrating a relatively soft and flexible polymeric material in theouter layer 14 improves the durability of thetubular member 10. Providing acatheter 30 having aballoon 36 with increased durability mitigates the likelihood of balloon burst due to puncture from a calcified vascular deposit or from a stent. - When utilized to form a portion of the
elongate shaft 32, themulti-layer tube 10 may have a wall thickness ranging from approximately 0.002 inches to 0.010 inches, and a length ranging from 10 cm to 150 cm. When utilized to form theballoon 36, themulti-layer tube 10 may have a wall thickness (post blow-molding) ranging from 0.0005 inches to 0.002 inches, and a length ranging from 1 cm to 10 cm. These dimensions are provided by way of example, not limitation. - The relative thickness and material composition of each
layer 12/14 may be modified to balance the respective properties of theelongate shaft 32 orballoon 36. For example, the thickness of the inner and outer layers of 12/14 may be modified and/or the materials selected for the inner andouter layers 12/14 may be modified. - Examples of suitable rigid polymers include polyurethane (isoplastic), aromatic polyamide, polyamide, PET, PEN, LCP, polycarbonate, aromatic polyester, etc. Examples of suitable soft and flexible polymers include polyurethane elastamers, polyether block amides (PEBA), Pellethane, Hytrel, Arnitel, Estane, Pebax, Grilamid, Vestamid, Riteflex, etc.
- A specific example of a hard-soft multiple-layer combination is one layer formed of a polyamide (e.g., nylon or PEBA) and another layer formed of polyethylene with a tie-layer of polyethylene copolymer disposed therebetween. Another specific example of a hard-soft multiple-layer combination is one layer formed of aromatic nylon and the other layer formed of
nylon 12. - The inner and/or
outer layers 12/14 may also comprise a reinforced polymer structure such as a polymer layer including continuous liquid crystal polymer fibers (LCP) dispersed in a non-LCP thermal plastic polymer matrix. The LCP content of the LCP containing layer may be greater than 0.1% by weight and less than 90% by weight. In addition, for enhanced performance, the LCP containing layer may comprise 0.05% to 50% by weight of the combined layers. - Refer now to FIG. 4 which illustrates an
extrusion system 100 for manufacturing the multi-layertubular member 10 discussed with reference to FIGS. 1 and 2.Extrusion system 100 includes one ormore extruders 50A/50B coupled to anextrusion head 40 as schematically illustrated byextrusion lines 60. Eachextruder 50A/50B includes ahopper 52, aheated barrel 56, anextrusion screw 58, and acontrol system 54. Thecontrol system 54 of eachextruder 50A/50B is operably coupled as indicated by dashedline 51 to facilitate co-extrusion. -
Extrusion head 40 includes an outer die portion 42 having a fixedportion 42F and arotatable portion 42R.Extrusion head 40 further includes arotatable pin 44 rotatably disposed in theouter die portions extrusion head 40 atinlets polymer entering inlet 48A forms theinner layer 12 and the moltenpolymer entering inlet 48B forms theouter layer 14 of themulti-layer extrusion 10. The molten polymer flows through the extrusion passages as indicated by the small arrows. The molten polymer exits theextrusion head 40 throughoutlet 46. Upon exiting theextrusion head 40 throughoutlet 46, the molten polymer begins to solidify to form themulti-layer tube 10 which may be subsequently cut to length or taken up byspool 80. - The
rotatable pin 44 is coupled to arotational drive 70A which rotates in the direction indicated byarrow 76A. Therotational drive 70A may comprise, for example, amotor 72 coupled to therotational pin 44 by a chain orbelt 74. Similarly, the rotationalouter die 42R is connected torotational drive 70B which rotates in the direction indicated byarrow 76B. Note that the direction of rotation ofdrive 70A is different than the rotational direction ofdrive 70B, thereby rotating thepin 44 in a different direction than theouter die 42R. - As the molten polymer exits the
extrusion head 40 throughoutlet 46, the rotatable outer die imparts helical orientation to theouter layer 14 of thetubular member 10. In addition, as the molten polymer exits theoutlet 46 of theextrusion head 40, the rotatingpin 44 imparts helical orientation to theinner layer 12 of thetubular member 10. Because thepin 44 is rotated in the opposite direction of rotatableouter die 42R, the helical orientation imparted to theouter layer 14 is in the opposite direction of the helical orientation imparted to theinner layer 12. Although not shown, an air passage may extend through thepin 44, which may be used to pump air into thetubular member 10 as it solidifies to help maintain thelumen 16 therein. As the molten polymer begins to solidify after exiting throughoutlet 46, the biaxial helical orientation imparted to the inner andouter layers 12/14 is locked into thetubular member 10. - Refer now to FIG. 5 which illustrates an
alternative extrusion system 200 for manufacturing the multi-layertubular member 10. Except as described herein, theextrusion system 200 is similar to the extrusion systems described in co-pending patent application ______ filed on even date herwith, entitled MEDICAL DEVICE WITH EXTRUDED MEMBER HAVING HELICAL ORIENTATION, the entire disclosure of which is hereby incorporated by reference. -
Extrusion system 200 includes two ormore extruders 50A/50B coupled toextrusion head 40 substantially as described previously. However, in this embodiment, thepin 44 remains stationary and is hollow to serve as a guide formandrel 90. Molten polymer enters theextrusion head 40 atinlets 48A/48B and flows through the extrusion passages as indicated by the small arrows. The molten polymer exits theextrusion head 40 throughoutlet 46. Upon exiting theextrusion head 40 throughoutlet 46, the molten polymer begins to solidify thereby creating a semi-molten polymer state. In a semi-molten state, the polymer typically has a temperature below the melting point but at or above the glass transition point. - In this semi-molten state, the multi-layer
tubular member 10 is rotated by rotational drive 70C in a direction indicated byarrow 76C. Thesupport mandrel 90 is also rotated by arotational drive 70A in a direction indicated byarrow 76A. Thesupport mandrel 90 and themulti-layered tubular member 10 are rotated in the same direction, while the rotational outer die 42R is rotated in the opposite direction byrotational drive 70B as indicated byarrow 76B. - By rotating the multi-layer
tubular member 10 in the semi-molten state, a molecular helical orientation is imparted to both theinner layer 12 and theouter layer 14. In particular, in the semi-molten state, the crystalline regions of the polymer are helically oriented by rotation and subsequently allowed to cool thereby locking in the biaxial helical orientation on the molecular level. Helical orientation is also imparted to the outertubular layer 14 in the opposite direction by virtue of the rotatingouter die 42R. The multi-layertubular member 10 may be cut into discrete lengths immediately after extrusion or spooled onto take-upspool 80A. If the multi-layertubular member 10 is taken-up byspool 80A, the multi-layertubular member 10 and thespool 80A may be rotated simultaneously. Similarly, if thesupport mandrel 90 is provided on aspool 80B, thespool 80B and thesupport mandrel 90 may be rotated simultaneously. - A further alternative extrusion system for manufacturing the multi-layer
tubular member 10 is partially disclosed in U.S. Pat. No. 5,622,665 to Wang, the entire disclosure of which is hereby incorporated by reference. Wang '665 discloses a method for making differential stiffness tubing for medical products, such as catheters. The method produces a tubing that has a stiff section and a flexible section joined by a relatively short transition section in which the materials of the stiff and flexible sections are wedged into each other in a smooth gradual manner to produce an inseparable bond between the materials without abrupt joints. The method also employs a resin modulating system that minimizes the length of the transition section by minimizing the volumes in all flow channels of the co-extrusion head used to produce the tubing. - Wang '665 further discloses a system for co-extruding differential stiffness tubing. The system includes a co-extrusion head into which extruders feed the different resins, such as a soft resin and a stiff resin, that will be used to form the finished tubing. A modulating device regulates the flow of the resins from each of the extruders into the co-extrusion head, while another modulator may be used to bleed resin “A” from the head to relieve residual pressure. To produce tubing with differential stiffness, the modulators are actuated periodically and in synchronized fashion to abruptly stop or change the resin flow to the head. Because of the design of co-extrusion head, the interface between the stiff resin and soft resin is naturally sheared and elongated when flowing through the flow channels of the head. Thus, these abrupt changes or stoppages by the modulators result in a very gradual change of stiff layer thickness in the tubing, creating the gradual stiffness change of the tubing. After discharge from the head, the tubing is cooled by passage through a water tank to form the tubing.
- The system disclosed by Wang '665 may be modified for purposes of the present invention. In particular, as with the extrusion system discussed with reference to FIG. 4 of the present application, a rotational drive may be coupled to the pin in the co-extrusion head of Wang '665, and a rotational drive may be coupled to the die of Wang '665, with the necessary modifications made to the co-extrusion head to permit such rotation. The rotational drives may comprise, for example, a motor coupled to the pin and die by a chain or belt. The direction of rotation of the pin drive is different than the rotational direction of the die drive, thereby rotating the pin in a different direction than the die.
- As the molten polymer exits the modified co-extrusion head of Wang '665, the rotatable die imparts helical orientation to the
outer layer 14 of thetubular member 10 and the rotatable pin imparts helical orientation to theinner layer 12 in the opposite direction. Although not shown, an air passage may extend through thepin 44, which may be used to pump air into thetubular member 10 as it solidifies to help maintain thelumen 16 therein. As the molten polymer begins to solidify after exiting through the modified extrusion head of Wang '665, the biaxial helical orientation imparted to the inner andouter layers 12/14 is locked into thetubular member 10. - Those skilled in the art will recognize that the present invention may be manifested in a variety of forms other than the specific embodiments described and contemplated herein. Accordingly, departures in form and detail may be made without departing from the scope and spirit of the present invention as described in the appended claims.
Claims (18)
1. A medical device comprising an extruded tubular polymer member, the tubular polymer member having an inner tubular layer and an outer tubular layer, wherein the inner tubular layer has helical orientation in a first direction and the outer tubular layer has helical orientation in a second direction different from the first direction.
2. A medical device as in claim 1 , wherein the tubular polymer member is made by an extrusion process including the step of extruding the polymer member through a rotating extrusion head over a counter-rotating mandrel.
3. A medical device as in claim 1 , wherein the tubular polymer member is made by an extrusion process including the step of rotating the polymer member after passing through a counter-rotating extrusion head.
4. A medical device as in claim 1 , wherein one of the inner and outer tubular layers is formed of a relatively flexible polymeric material and the other of the inner and outer tubular layers is formed of a relatively rigid polymeric material.
5. A medical device as in claim 1 , wherein one of the inner and outer tubular layers is formed of continuous LCP fibers dispersed in a non-LCP polymer matrix.
6. A medical device as in claim 5 , wherein the LCP content of the LCP containing layer is between 0.1% and 90% by weight.
7. A medical device as in claim 5 , wherein the LCP containing layer comprises 0.05% to 50% by weight of the combined layers.
8. A medical device comprising an extruded tubular polymer member formed of a relatively rigid polymeric tubular layer and a relatively flexible polymeric tubular layer, wherein the relatively rigid polymeric tubular layer has helical orientation in a first direction and the relatively flexible polymeric tubular layer has helical orientation in a second direction different from the first direction.
9. A medical device as in claim 8 , wherein the helical orientation is formed by an extrusion process including the step of extruding the polymer member through a rotating extrusion head over a counter-rotating mandrel.
10. A medical device as in claim 8 , wherein the helical orientation is formed by an extrusion process including the step of rotating the polymer member after passing through a counter-rotating extrusion head.
11. A medical device comprising an extruded tubular polymer member, the tubular polymer member comprising a first extruded tubular polymer layer and a second extruded tubular polymer layer, the first extruded tubular polymer layer including continuous LCP fibers dispersed in a non-LCP thermoplastic polymer matrix, wherein the first extruded polymer layer has helical orientation in a first direction and the second extruded polymer layer has helical orientation in a second direction different from the first direction.
12. A medical device as in claim 11 , wherein the helical orientation is formed by an extrusion process including the step of extruding the polymer member through a rotating extrusion head over a counter-rotating mandrel.
13. A medical device as in claim 11 , wherein the helical orientation is formed by an extrusion process including the step of rotating the polymer member after passing through a counter-rotating extrusion head.
14. A medical device as in claim 11 , wherein the LCP content of the LCP containing layer is between 0.1% and 90% by weight.
15. A medical device as in claim 11 , wherein the LCP containing layer comprises 0.5% to 50% by weight of the combined layers.
16. A method of making a medical tubular polymer member by rotating the polymer member after passing through a counter-rotating extrusion head.
17. An intravascular catheter including a shaft comprising a tubular polymer member formed by the method of claim 16 .
18. An intravascular catheter including an inflatable balloon comprising a tubular polymer member formed by the method of claim 16.
Priority Applications (6)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US09/898,717 US20030009151A1 (en) | 2001-07-03 | 2001-07-03 | Biaxially oriented multilayer polymer tube for medical devices |
CA2452303A CA2452303C (en) | 2001-07-03 | 2002-05-01 | Biaxially oriented multilayer polymer tube for medical devices |
EP02729123A EP1401629A1 (en) | 2001-07-03 | 2002-05-01 | Biaxially oriented multilayer polymer tube for medical devices |
JP2003510239A JP4472331B2 (en) | 2001-07-03 | 2002-05-01 | Extrusion system for forming biaxially oriented multilayer polymer tubes used in medical devices |
PCT/US2002/014017 WO2003004248A1 (en) | 2001-07-03 | 2002-05-01 | Biaxially oriented multilayer polymer tube for medical devices |
US10/335,743 US7128862B2 (en) | 2001-07-03 | 2003-01-02 | Biaxially oriented multilayer polymer tube for medical devices |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US09/898,717 US20030009151A1 (en) | 2001-07-03 | 2001-07-03 | Biaxially oriented multilayer polymer tube for medical devices |
Related Child Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/335,743 Continuation US7128862B2 (en) | 2001-07-03 | 2003-01-02 | Biaxially oriented multilayer polymer tube for medical devices |
Publications (1)
Publication Number | Publication Date |
---|---|
US20030009151A1 true US20030009151A1 (en) | 2003-01-09 |
Family
ID=25409940
Family Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/898,717 Abandoned US20030009151A1 (en) | 2001-07-03 | 2001-07-03 | Biaxially oriented multilayer polymer tube for medical devices |
US10/335,743 Expired - Fee Related US7128862B2 (en) | 2001-07-03 | 2003-01-02 | Biaxially oriented multilayer polymer tube for medical devices |
Family Applications After (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/335,743 Expired - Fee Related US7128862B2 (en) | 2001-07-03 | 2003-01-02 | Biaxially oriented multilayer polymer tube for medical devices |
Country Status (5)
Country | Link |
---|---|
US (2) | US20030009151A1 (en) |
EP (1) | EP1401629A1 (en) |
JP (1) | JP4472331B2 (en) |
CA (1) | CA2452303C (en) |
WO (1) | WO2003004248A1 (en) |
Cited By (24)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20030165647A1 (en) * | 2002-03-04 | 2003-09-04 | Terumo Kabushiki Kaisha | Medical tubing and extrusion die for producing the same |
WO2005003300A2 (en) * | 2003-06-04 | 2005-01-13 | University Of South Carolina | Tissue scaffold having aligned fibrils, apparatus and method for producing same, and methods of using same |
US20060011251A1 (en) * | 2002-11-21 | 2006-01-19 | Masatomi Sato | Multilayer tube |
US20070208300A1 (en) * | 2006-03-01 | 2007-09-06 | Applied Medical Resources Corporation | Gas insufflation and suction/irrigation tubing |
US20070270941A1 (en) * | 2006-05-17 | 2007-11-22 | Headley F Anthony | Bioabsorbable stents with reinforced filaments |
US20080045928A1 (en) * | 2006-06-30 | 2008-02-21 | Abbott Cardiovascular System Inc. | Balloon catheter tapered shaft having high strength and flexibility and method of making same |
US20090156998A1 (en) * | 2007-12-17 | 2009-06-18 | Abbott Cardiovascular Systems Inc. | Catheter having transitioning shaft segments |
US20100130926A1 (en) * | 2008-11-26 | 2010-05-27 | Abbott Cardiovascular Systems, Inc. | Robust catheter tubing |
US20100130927A1 (en) * | 2008-11-26 | 2010-05-27 | Abbott Cardiovascular Systems Inc. | Low compliant catheter tubing |
US20100130925A1 (en) * | 2008-11-26 | 2010-05-27 | Abbott Cardiovascular Systems, Inc. | Robust catheter tubing |
EP2215962A1 (en) * | 2009-02-09 | 2010-08-11 | FUJIFILM Corporation | Method for production of flexible tube for endoscope |
US20100233404A1 (en) * | 2003-07-10 | 2010-09-16 | Boston Scientific Scimed, Inc. | Medical device tubing with discrete orientation regions |
US20110079941A1 (en) * | 2004-07-26 | 2011-04-07 | Bin Huang | Method of fabricating an implantable medical device with biaxially oriented polymers |
US7951116B2 (en) | 2004-11-12 | 2011-05-31 | Boston Scientific Scimed, Inc. | Selective surface modification of catheter tubing |
US20120192987A1 (en) * | 2011-01-27 | 2012-08-02 | Carefusion 303, Inc. | Low permeability silicone rubber tubing |
US8684963B2 (en) | 2012-07-05 | 2014-04-01 | Abbott Cardiovascular Systems Inc. | Catheter with a dual lumen monolithic shaft |
US20150108693A1 (en) * | 2008-11-17 | 2015-04-23 | Xyleco, Inc. | Processing biomass |
CN105034308A (en) * | 2015-07-27 | 2015-11-11 | 联塑科技发展(武汉)有限公司 | Novel processing method and system for PVC pipe |
US9517149B2 (en) | 2004-07-26 | 2016-12-13 | Abbott Cardiovascular Systems Inc. | Biodegradable stent with enhanced fracture toughness |
CN107351354A (en) * | 2017-07-10 | 2017-11-17 | 四川大学 | The tube extruding machine head for the three-layer plastic multiple tube that intermediate layer fiber is circumferentially orientated |
US9855400B2 (en) | 2001-09-19 | 2018-01-02 | Abbott Cardiovascular Systems, Inc. | Catheter with a multilayered shaft section having a polyimide layer |
US20190246883A1 (en) * | 2018-02-14 | 2019-08-15 | Fadi N. Bashour | Alimentary Engagement Device |
US10406329B2 (en) | 2011-05-26 | 2019-09-10 | Abbott Cardiovascular Systems, Inc. | Through tip for catheter |
US20200406019A1 (en) * | 2018-03-29 | 2020-12-31 | Ypsomed Ag | Multi-layer hose for an infustion set for dispensing a fluid |
Families Citing this family (48)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6379334B1 (en) | 1997-02-10 | 2002-04-30 | Essex Technology, Inc. | Rotate advance catheterization system |
WO2001023027A1 (en) | 1999-09-27 | 2001-04-05 | Essex Technology, Inc. | Rotate-to-advance catheterization system |
US6776945B2 (en) * | 2001-07-03 | 2004-08-17 | Scimed Life Systems, Inc. | Medical device with extruded member having helical orientation |
PT1673114E (en) * | 2003-10-17 | 2008-10-17 | Invatec Srl | Catheter balloons |
US8353867B2 (en) * | 2004-05-04 | 2013-01-15 | Boston Scientific Scimed, Inc. | Medical devices |
US7338271B2 (en) * | 2004-05-19 | 2008-03-04 | Cangen Holdings, Inc. | Extrusion head having a rotating die |
US20070276354A1 (en) * | 2004-07-21 | 2007-11-29 | Cook Incorporated | Introducer Sheath and Method for Making |
JP4647299B2 (en) * | 2004-12-09 | 2011-03-09 | 株式会社カネカ | Medical catheter tube and manufacturing method thereof |
EP1861133B1 (en) | 2005-02-28 | 2012-11-21 | Spirus Medical Inc. | Rotate-to-advance catheterization system |
US8317678B2 (en) | 2005-05-04 | 2012-11-27 | Olympus Endo Technology America Inc. | Rotate-to-advance catheterization system |
US8414477B2 (en) | 2005-05-04 | 2013-04-09 | Olympus Endo Technology America Inc. | Rotate-to-advance catheterization system |
US8235942B2 (en) | 2005-05-04 | 2012-08-07 | Olympus Endo Technology America Inc. | Rotate-to-advance catheterization system |
US8343040B2 (en) | 2005-05-04 | 2013-01-01 | Olympus Endo Technology America Inc. | Rotate-to-advance catheterization system |
US7780650B2 (en) | 2005-05-04 | 2010-08-24 | Spirus Medical, Inc. | Rotate-to-advance catheterization system |
US7513766B2 (en) * | 2005-10-11 | 2009-04-07 | Cryovac, Inc. | Extrusion apparatus having a driven feed segment |
CA2633578A1 (en) | 2005-12-16 | 2007-07-05 | Interface Associates, Inc. | Multi-layer balloons for medical applications and methods for manufacturing the same |
US20070162110A1 (en) * | 2006-01-06 | 2007-07-12 | Vipul Bhupendra Dave | Bioabsorbable drug delivery devices |
US20070158880A1 (en) * | 2006-01-06 | 2007-07-12 | Vipul Bhupendra Dave | Methods of making bioabsorbable drug delivery devices comprised of solvent cast tubes |
US20070160672A1 (en) * | 2006-01-06 | 2007-07-12 | Vipul Bhupendra Dave | Methods of making bioabsorbable drug delivery devices comprised of solvent cast films |
US8574220B2 (en) | 2006-02-28 | 2013-11-05 | Olympus Endo Technology America Inc. | Rotate-to-advance catheterization system |
US8435229B2 (en) | 2006-02-28 | 2013-05-07 | Olympus Endo Technology America Inc. | Rotate-to-advance catheterization system |
EP2023869B1 (en) * | 2006-05-12 | 2019-09-18 | Cardinal Health Switzerland 515 GmbH | Balloon expandable bioabsorbable drug eluting flexible stent |
US20080097491A1 (en) * | 2006-08-28 | 2008-04-24 | Fred Gobel | Tissue to tissue anchoring device and method of using the same |
US8870755B2 (en) | 2007-05-18 | 2014-10-28 | Olympus Endo Technology America Inc. | Rotate-to-advance catheterization system |
US7972373B2 (en) * | 2007-12-19 | 2011-07-05 | Advanced Technologies And Regenerative Medicine, Llc | Balloon expandable bioabsorbable stent with a single stress concentration region interconnecting adjacent struts |
US8057876B2 (en) * | 2008-02-25 | 2011-11-15 | Abbott Cardiovascular Systems Inc. | Bioabsorbable stent with layers having different degradation rates |
US9265918B2 (en) | 2008-09-03 | 2016-02-23 | Boston Scientific Scimed, Inc. | Multilayer medical balloon |
KR20140037793A (en) * | 2010-10-19 | 2014-03-27 | 아이2아이씨 코포레이션 | Apparatus and method of manufacturing objects with varying concentration of particles |
KR102182896B1 (en) | 2012-03-09 | 2020-11-26 | 클리어스트림 테크놀러지스 리미티드 | Parison for forming blow molded medical balloon with midified portion, medical balloon, and related methods |
US8853344B2 (en) | 2012-11-09 | 2014-10-07 | Ticona Llc | Liquid crystalline polymer composition for films |
LT2916901T (en) | 2012-11-12 | 2020-10-12 | Hollister Incorporated | Intermittent catheter assembly |
LT2919825T (en) | 2012-11-14 | 2018-12-10 | Hollister Incorporated | Disposable catheter with selectively degradable inner core |
NZ717730A (en) * | 2013-08-28 | 2020-02-28 | Clearstream Tech Ltd | Apparatuses and methods for providing radiopaque medical balloons |
HUE063905T2 (en) | 2013-11-08 | 2024-02-28 | Hollister Inc | Oleophilic lubricated catheters |
CA2923676C (en) | 2013-12-12 | 2020-10-13 | Hollister Incorporated | Flushable catheters |
DK3079748T3 (en) | 2013-12-12 | 2020-08-17 | Hollister Inc | EXCLUSIVE DECOMPOSITION CATHETER |
AU2014362368B2 (en) | 2013-12-12 | 2018-10-04 | Hollister Incorporated | Flushable catheters |
AU2014362360B2 (en) | 2013-12-12 | 2020-01-02 | Hollister Incorporated | Flushable catheters |
RU2719979C1 (en) * | 2014-08-28 | 2020-04-23 | Клиарстрим Текнолоджис Лимитед | Device and methods for producing radiopaque medical balloons |
US10363399B2 (en) | 2014-09-30 | 2019-07-30 | Boston Scientific Scimed, Inc. | Dual-layer balloon design and method of making the same |
JP6523727B2 (en) * | 2015-03-20 | 2019-06-05 | テルモ株式会社 | catheter |
CA2989330C (en) | 2015-06-17 | 2023-01-31 | Hollister Incorporated | Selectively water disintegrable materials and catheters made of such materials |
US10952702B2 (en) * | 2016-06-21 | 2021-03-23 | Canon U.S.A., Inc. | Non-uniform rotational distortion detection catheter system |
KR102168072B1 (en) * | 2017-12-05 | 2020-10-20 | 이제권 | Balloon catheter manufacturing method |
KR102291285B1 (en) * | 2020-07-07 | 2021-08-20 | (주)동부화학 | Blow-extrusion molding device with rotating safety parts and film produced by the device |
US11911949B2 (en) * | 2021-07-27 | 2024-02-27 | Wisconsin Alumni Research Foundation | Rotating nozzle structure and method |
KR102612673B1 (en) * | 2023-06-12 | 2023-12-14 | 주식회사 에스엠케미칼 | Method, apparatus and system for manufacturing a recyclable cosmetic container using polypropylene material |
KR102612676B1 (en) * | 2023-06-12 | 2023-12-14 | 주식회사 에스엠케미칼 | Method, apparatus and system for manufacturing a recyclable cosmetic container using recycled low-density polyethylene material |
Family Cites Families (47)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US594957A (en) * | 1897-12-07 | Half to william e | ||
US2616126A (en) * | 1950-06-29 | 1952-11-04 | Us Rubber Co | Plastic tube manufacture |
US3281897A (en) * | 1963-02-15 | 1966-11-01 | Plastic Textile Access Ltd | Extruded plastic tubing |
US3404203A (en) * | 1963-05-03 | 1968-10-01 | Dow Chemical Co | Method of extruding bi-helically oriented thermoplastic tube |
US3279501A (en) * | 1965-01-28 | 1966-10-18 | Dow Chemical Co | Extrusion and product |
US3759647A (en) * | 1969-04-10 | 1973-09-18 | Turner Alfrey Us | Apparatus for the preparation of multilayer plastic articles |
US3565985A (en) * | 1969-04-10 | 1971-02-23 | Dow Chemical Co | Method of preparing multilayer plastic articles |
US3647612A (en) * | 1969-06-06 | 1972-03-07 | Dow Chemical Co | Multilayer plastic articles |
US3651187A (en) * | 1969-10-16 | 1972-03-21 | Hercules Inc | Extrusion process |
US3933960A (en) * | 1970-09-11 | 1976-01-20 | Btr Industries Limited | Method of extruding fiber reinforced plural layered plastic tubes |
JPS5338306B2 (en) * | 1972-03-31 | 1978-10-14 | ||
US3989785A (en) * | 1972-11-21 | 1976-11-02 | The Dow Chemical Company | Method for the preparation of plastic film |
US4039364A (en) * | 1974-07-05 | 1977-08-02 | Rasmussen O B | Method for producing a laminated high strength sheet |
US4793885A (en) * | 1974-12-11 | 1988-12-27 | Rasmussen O B | Method of laminating and stretching film material and apparatus for said method |
IN144765B (en) * | 1975-02-12 | 1978-07-01 | Rasmussen O B | |
AR219554A1 (en) * | 1978-10-17 | 1980-08-29 | Singer Aronovici A | MANUFACTURING PROCEDURE FOR A FILM OF MULTIPLE CROSSED STRATA AND PRODUCT OBTAINED |
DE2910749C2 (en) * | 1979-03-19 | 1982-11-25 | Dr. Eduard Fresenius, Chemisch-pharmazeutische Industrie KG, 6380 Bad Homburg | Catheter with contrast stripes |
US4657024A (en) * | 1980-02-04 | 1987-04-14 | Teleflex Incorporated | Medical-surgical catheter |
FR2591527B1 (en) * | 1985-12-18 | 1988-04-01 | Alphacan Sa | APPARATUS FOR EXECUTING PLASTIC TUBES WITH COMPOSITE WALLS. PROCESS FOR THE MANUFACTURE OF TUBES USING THE APPARATUS |
JPH0829560B2 (en) * | 1987-02-13 | 1996-03-27 | 三菱化学株式会社 | Multi-layer film molding method |
US4883622A (en) * | 1987-09-17 | 1989-11-28 | Canadian Patents And Development Limited | Method of manufacturing discrete fiber reinforced, plastic tube and apparatus therefor |
US4885196A (en) * | 1988-06-07 | 1989-12-05 | Mobil Oil Corporation | Three-layer cross-laminated film with foam core made by counter-rotating dies |
US6045737A (en) * | 1989-06-16 | 2000-04-04 | Superex Polymer, Inc. | Coextrusion of liquid crystal polymers and thermoplastic polymers |
US5156785A (en) * | 1991-07-10 | 1992-10-20 | Cordis Corporation | Extruded tubing and catheters having increased rotational stiffness |
US5248305A (en) * | 1989-08-04 | 1993-09-28 | Cordis Corporation | Extruded tubing and catheters having helical liquid crystal fibrils |
US5059375A (en) * | 1989-11-13 | 1991-10-22 | Minnesota Mining & Manufacturing Company | Apparatus and method for producing kink resistant tubing |
US4990143A (en) * | 1990-04-09 | 1991-02-05 | Sheridan Catheter Corporation | Reinforced medico-surgical tubes |
NL9300572A (en) * | 1993-03-31 | 1994-10-17 | Cordis Europ | Method for manufacturing an extrusion profile with length-varying properties and catheter manufactured therewith. |
NL9400031A (en) * | 1994-01-07 | 1995-08-01 | Cordis Europ | Method for manufacturing a tubular extrusion profile and catheter made therefrom. |
US5505887A (en) * | 1994-03-10 | 1996-04-09 | Meadox Medicals, Inc. | Extrusion process for manufacturing PTFE products |
WO1995029051A1 (en) | 1994-04-20 | 1995-11-02 | Wang James C | Extrusion head and system |
US5533985A (en) * | 1994-04-20 | 1996-07-09 | Wang; James C. | Tubing |
JP4408958B2 (en) * | 1995-02-28 | 2010-02-03 | ボストン サイエンティフィック コーポレーション | Medical instruments |
US5882741A (en) * | 1996-01-26 | 1999-03-16 | Foster-Miller, Inc. | Members having a multiaxially oriented coating of thermotropic liquid crystalline polymer and method and apparatus for producing such members |
GB9604127D0 (en) | 1996-02-27 | 1996-05-01 | Alpha Marathon Mfg | Multi-layer blown-film extrusion dye |
US6436056B1 (en) * | 1996-02-28 | 2002-08-20 | Boston Scientific Corporation | Polymeric implements for torque transmission |
US6124007A (en) * | 1996-03-06 | 2000-09-26 | Scimed Life Systems Inc | Laminate catheter balloons with additive burst strength and methods for preparation of same |
US5899892A (en) * | 1996-05-31 | 1999-05-04 | Scimed Life Systems, Inc. | Catheter having distal fiber braid |
US5947940A (en) * | 1997-06-23 | 1999-09-07 | Beisel; Robert F. | Catheter reinforced to prevent luminal collapse and tensile failure thereof |
US6284333B1 (en) | 1997-09-10 | 2001-09-04 | Scimed Life Systems, Inc. | Medical devices made from polymer blends containing low melting temperature liquid crystal polymers |
US6242063B1 (en) * | 1997-09-10 | 2001-06-05 | Scimed Life Systems, Inc. | Balloons made from liquid crystal polymer blends |
US6405974B1 (en) * | 1998-08-12 | 2002-06-18 | F. John Herrington | Ribbed core dual wall structure |
CA2358661A1 (en) | 1999-01-20 | 2000-07-27 | Boston Scientific Limited | Intravascular catheter with composite reinforcement |
US6171295B1 (en) * | 1999-01-20 | 2001-01-09 | Scimed Life Systems, Inc. | Intravascular catheter with composite reinforcement |
JP2001309533A (en) * | 2000-04-18 | 2001-11-02 | Tokiwa Chemical Industry Co Ltd | Coil for cable installation and manufacturing method therefor |
US6776945B2 (en) * | 2001-07-03 | 2004-08-17 | Scimed Life Systems, Inc. | Medical device with extruded member having helical orientation |
ATE447423T1 (en) * | 2002-03-04 | 2009-11-15 | Terumo Corp | MEDICAL HOSE AND EXTRUSION NOZZLE FOR PRODUCING IT |
-
2001
- 2001-07-03 US US09/898,717 patent/US20030009151A1/en not_active Abandoned
-
2002
- 2002-05-01 JP JP2003510239A patent/JP4472331B2/en not_active Expired - Fee Related
- 2002-05-01 WO PCT/US2002/014017 patent/WO2003004248A1/en active Application Filing
- 2002-05-01 EP EP02729123A patent/EP1401629A1/en not_active Withdrawn
- 2002-05-01 CA CA2452303A patent/CA2452303C/en not_active Expired - Fee Related
-
2003
- 2003-01-02 US US10/335,743 patent/US7128862B2/en not_active Expired - Fee Related
Cited By (71)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US9855400B2 (en) | 2001-09-19 | 2018-01-02 | Abbott Cardiovascular Systems, Inc. | Catheter with a multilayered shaft section having a polyimide layer |
EP1344549A1 (en) * | 2002-03-04 | 2003-09-17 | Terumo Kabushiki Kaisha | Medical tubing and extrusion die for producing the same |
US20030165647A1 (en) * | 2002-03-04 | 2003-09-04 | Terumo Kabushiki Kaisha | Medical tubing and extrusion die for producing the same |
US20060011251A1 (en) * | 2002-11-21 | 2006-01-19 | Masatomi Sato | Multilayer tube |
US7338517B2 (en) | 2003-06-04 | 2008-03-04 | University Of South Carolina | Tissue scaffold having aligned fibrils and artificial tissue comprising the same |
WO2005003300A3 (en) * | 2003-06-04 | 2005-07-28 | Univ South Carolina | Tissue scaffold having aligned fibrils, apparatus and method for producing same, and methods of using same |
WO2005003300A2 (en) * | 2003-06-04 | 2005-01-13 | University Of South Carolina | Tissue scaffold having aligned fibrils, apparatus and method for producing same, and methods of using same |
US7878786B2 (en) | 2003-06-04 | 2011-02-01 | University Of South Carolina | Apparatus for producing tissue scaffold having aligned fibrils |
US7727441B2 (en) | 2003-06-04 | 2010-06-01 | University Of South Carolina | Method for producing tissue scaffold having aligned fibrils |
US8304050B2 (en) * | 2003-07-10 | 2012-11-06 | Boston Scientific Scimed, Inc. | Medical device tubing with discrete orientation regions |
US20100233404A1 (en) * | 2003-07-10 | 2010-09-16 | Boston Scientific Scimed, Inc. | Medical device tubing with discrete orientation regions |
US8192678B2 (en) * | 2004-07-26 | 2012-06-05 | Advanced Cardiovascular Systems, Inc. | Method of fabricating an implantable medical device with biaxially oriented polymers |
US20140228929A1 (en) * | 2004-07-26 | 2014-08-14 | Abbott Cardiovascular Systems Inc. | Implantable medical device with biaxially oriented polymers |
US9517149B2 (en) | 2004-07-26 | 2016-12-13 | Abbott Cardiovascular Systems Inc. | Biodegradable stent with enhanced fracture toughness |
US20110079941A1 (en) * | 2004-07-26 | 2011-04-07 | Bin Huang | Method of fabricating an implantable medical device with biaxially oriented polymers |
US8715564B2 (en) | 2004-07-26 | 2014-05-06 | Advanced Cardiovascular Systems, Inc. | Method of fabricating an implantable medical device with biaxially oriented polymers |
US9132257B2 (en) | 2004-11-12 | 2015-09-15 | Boston Scientific Scimed, Inc. | Selective surface modification of catheter tubing |
US8777928B2 (en) | 2004-11-12 | 2014-07-15 | Boston Scientific Scimed, Inc. | Selective surface modification of catheter tubing |
US7951116B2 (en) | 2004-11-12 | 2011-05-31 | Boston Scientific Scimed, Inc. | Selective surface modification of catheter tubing |
US20110230860A1 (en) * | 2004-11-12 | 2011-09-22 | Boston Scientific Scimed, Inc. | Selective surface modification of catheter tubing |
US9962537B2 (en) | 2006-03-01 | 2018-05-08 | Applied Medical Resources Corporation | Gas insufflation and suction/irrigation tubing |
US20070208300A1 (en) * | 2006-03-01 | 2007-09-06 | Applied Medical Resources Corporation | Gas insufflation and suction/irrigation tubing |
US20100213634A1 (en) * | 2006-05-17 | 2010-08-26 | Boston Scientific Scimed, Inc. | Bioabsorbable stents with reinforced filaments |
US8753387B2 (en) | 2006-05-17 | 2014-06-17 | Boston Scientific Scimed, Inc. | Bioabsorbable stents with reinforced filaments |
US20090315208A1 (en) * | 2006-05-17 | 2009-12-24 | Boston Scientific Scimed, Inc. | Bioabsorbable stents with reinforced filaments |
US7594928B2 (en) * | 2006-05-17 | 2009-09-29 | Boston Scientific Scimed, Inc. | Bioabsorbable stents with reinforced filaments |
US9320625B2 (en) | 2006-05-17 | 2016-04-26 | Boston Scientific Scimed, Inc. | Bioabsorbable stents with reinforced filaments |
US8101104B2 (en) | 2006-05-17 | 2012-01-24 | Boston Scientific Scimed, Inc. | Process of making a stent |
US20070270941A1 (en) * | 2006-05-17 | 2007-11-22 | Headley F Anthony | Bioabsorbable stents with reinforced filaments |
US10245352B2 (en) * | 2006-06-30 | 2019-04-02 | Abbott Cardiovascular Systems Inc. | Catheter shaft having high strength and flexibility |
US8721624B2 (en) | 2006-06-30 | 2014-05-13 | Abbott Cardiovascular Systems Inc. | Balloon catheter shaft having high strength and flexibility |
US8388602B2 (en) | 2006-06-30 | 2013-03-05 | Abbott Cardiovascular Systems Inc. | Balloon catheter shaft having high strength and flexibility |
US20080045928A1 (en) * | 2006-06-30 | 2008-02-21 | Abbott Cardiovascular System Inc. | Balloon catheter tapered shaft having high strength and flexibility and method of making same |
US9056190B2 (en) | 2006-06-30 | 2015-06-16 | Abbott Cardiovascular Systems Inc. | Balloon catheter tapered shaft having high strength and flexibility and method of making same |
US8382738B2 (en) | 2006-06-30 | 2013-02-26 | Abbott Cardiovascular Systems, Inc. | Balloon catheter tapered shaft having high strength and flexibility and method of making same |
US20140213967A1 (en) * | 2006-06-30 | 2014-07-31 | Abbott Cardiovascular Systems Inc. | Balloon Catheter Shaft Having High Strength and Flexibility |
US9205223B2 (en) * | 2006-06-30 | 2015-12-08 | Abbott Cardiovascular Systems Inc | Balloon catheter shaft having high strength and flexibility |
US9968713B2 (en) | 2006-06-30 | 2018-05-15 | Abbott Cardiovascular Systems Inc. | Balloon catheter shaft having high strength and flexibility |
US9468744B2 (en) | 2007-12-17 | 2016-10-18 | Abbott Cardiovascular Systems Inc. | Catheter having transitioning shaft segments |
US8657782B2 (en) | 2007-12-17 | 2014-02-25 | Abbott Cardiovascular Systems, Inc. | Catheter having transitioning shaft segments |
US20090156998A1 (en) * | 2007-12-17 | 2009-06-18 | Abbott Cardiovascular Systems Inc. | Catheter having transitioning shaft segments |
US8403885B2 (en) | 2007-12-17 | 2013-03-26 | Abbott Cardiovascular Systems Inc. | Catheter having transitioning shaft segments |
US9216274B2 (en) | 2007-12-17 | 2015-12-22 | Abbott Cardiovascular Systems Inc. | Catheter having transitioning shaft segments |
US9586341B2 (en) | 2008-11-17 | 2017-03-07 | Xyleco, Inc. | Processing biomass |
US9321850B2 (en) * | 2008-11-17 | 2016-04-26 | Xyleco, Inc. | Processing biomass |
US20150108693A1 (en) * | 2008-11-17 | 2015-04-23 | Xyleco, Inc. | Processing biomass |
CN105524949A (en) * | 2008-11-17 | 2016-04-27 | 希乐克公司 | Biomass processing |
CN105420287A (en) * | 2008-11-17 | 2016-03-23 | 希乐克公司 | biomass processing |
US8444608B2 (en) * | 2008-11-26 | 2013-05-21 | Abbott Cardivascular Systems, Inc. | Robust catheter tubing |
US9669196B2 (en) | 2008-11-26 | 2017-06-06 | Abbott Cardiovascular Systems, Inc. | Robust multi-layer balloon |
US20100130926A1 (en) * | 2008-11-26 | 2010-05-27 | Abbott Cardiovascular Systems, Inc. | Robust catheter tubing |
US20100130927A1 (en) * | 2008-11-26 | 2010-05-27 | Abbott Cardiovascular Systems Inc. | Low compliant catheter tubing |
US8613722B2 (en) | 2008-11-26 | 2013-12-24 | Abbott Cardiovascular Systems, Inc. | Robust multi-layer balloon |
US20100130925A1 (en) * | 2008-11-26 | 2010-05-27 | Abbott Cardiovascular Systems, Inc. | Robust catheter tubing |
US9381325B2 (en) | 2008-11-26 | 2016-07-05 | Abbott Cadiovascular Systems, Inc. | Robust catheter tubing |
US8070719B2 (en) * | 2008-11-26 | 2011-12-06 | Abbott Cardiovascular Systems, Inc. | Low compliant catheter tubing |
US8052638B2 (en) | 2008-11-26 | 2011-11-08 | Abbott Cardiovascular Systems, Inc. | Robust multi-layer balloon |
US9539368B2 (en) | 2008-11-26 | 2017-01-10 | Abbott Cardiovascular Systems, Inc. | Robust catheter tubing |
US20100201029A1 (en) * | 2009-02-09 | 2010-08-12 | Fujifilm Corporation | Method for production of flexible tube for endoscope |
EP2215962A1 (en) * | 2009-02-09 | 2010-08-11 | FUJIFILM Corporation | Method for production of flexible tube for endoscope |
US9192754B2 (en) * | 2011-01-27 | 2015-11-24 | Carefusion 303, Inc. | Low permeability silicone rubber tubing |
US20120192987A1 (en) * | 2011-01-27 | 2012-08-02 | Carefusion 303, Inc. | Low permeability silicone rubber tubing |
US11383070B2 (en) | 2011-05-26 | 2022-07-12 | Abbott Cardiovascular Systems Inc. | Through tip for catheter |
US10406329B2 (en) | 2011-05-26 | 2019-09-10 | Abbott Cardiovascular Systems, Inc. | Through tip for catheter |
US8684963B2 (en) | 2012-07-05 | 2014-04-01 | Abbott Cardiovascular Systems Inc. | Catheter with a dual lumen monolithic shaft |
US9707380B2 (en) | 2012-07-05 | 2017-07-18 | Abbott Cardiovascular Systems Inc. | Catheter with a dual lumen monolithic shaft |
CN105034308A (en) * | 2015-07-27 | 2015-11-11 | 联塑科技发展(武汉)有限公司 | Novel processing method and system for PVC pipe |
CN107351354A (en) * | 2017-07-10 | 2017-11-17 | 四川大学 | The tube extruding machine head for the three-layer plastic multiple tube that intermediate layer fiber is circumferentially orientated |
US20190246883A1 (en) * | 2018-02-14 | 2019-08-15 | Fadi N. Bashour | Alimentary Engagement Device |
US10827909B2 (en) * | 2018-02-14 | 2020-11-10 | Marla F. Bashour | Alimentary engagement device |
US20200406019A1 (en) * | 2018-03-29 | 2020-12-31 | Ypsomed Ag | Multi-layer hose for an infustion set for dispensing a fluid |
Also Published As
Publication number | Publication date |
---|---|
EP1401629A1 (en) | 2004-03-31 |
US20030100869A1 (en) | 2003-05-29 |
US7128862B2 (en) | 2006-10-31 |
JP4472331B2 (en) | 2010-06-02 |
CA2452303A1 (en) | 2003-01-16 |
WO2003004248A1 (en) | 2003-01-16 |
JP2005519649A (en) | 2005-07-07 |
CA2452303C (en) | 2011-03-15 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US7128862B2 (en) | Biaxially oriented multilayer polymer tube for medical devices | |
CA2456810C (en) | Medical device with extruded member having helical orientation | |
EP1344549B1 (en) | Medical tubing and extrusion die for producing the same | |
JP3163106B2 (en) | Multilumen catheter | |
US7037295B2 (en) | Co-extruded taper shaft | |
US5622665A (en) | Method for making tubing | |
US6511462B1 (en) | Catheter and method of manufacturing the same | |
US6024722A (en) | Thermoplastic polyimide balloon catheter construction | |
US6977103B2 (en) | Dimensionally stable balloons | |
US5156785A (en) | Extruded tubing and catheters having increased rotational stiffness | |
US6596219B2 (en) | Inflatable member formed of liquid crystal polymeric material blend | |
US6443925B1 (en) | Balloon catheter shaft formed of liquid crystal polymeric material blend | |
US20040215223A1 (en) | Cutting stent and balloon | |
US20050234500A1 (en) | Dimensionally stable balloons | |
WO2003072178A1 (en) | Medical device | |
US7101597B2 (en) | Medical devices made from polymer blends containing low melting temperature liquid crystal polymers | |
US20080319389A1 (en) | Medical Devices with Rigid Rod Paraphenylene | |
CA2347024C (en) | Method for making tubing |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AS | Assignment |
Owner name: SCIMED LIFE SYSTEMS, INC., MINNESOTA Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:WANG, LIXIAO;REEL/FRAME:011974/0660 Effective date: 20010619 |
|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |