WO2003045280A1 - Helical insert for a conduit - Google Patents

Helical insert for a conduit Download PDF

Info

Publication number
WO2003045280A1
WO2003045280A1 PCT/GB2002/005276 GB0205276W WO03045280A1 WO 2003045280 A1 WO2003045280 A1 WO 2003045280A1 GB 0205276 W GB0205276 W GB 0205276W WO 03045280 A1 WO03045280 A1 WO 03045280A1
Authority
WO
WIPO (PCT)
Prior art keywords
insert
stent
longitudinally extending
helix
extending member
Prior art date
Application number
PCT/GB2002/005276
Other languages
French (fr)
Inventor
John Graeme Houston
Robert Gordon Hood
John Bruce Cameron Dick
Craig Mcleod Duff
Allana Johnstone
Christophe Emmanuel Sarran
Peter A. Stonebridge
Original Assignee
Tayside Flow Technologies Limited
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Tayside Flow Technologies Limited filed Critical Tayside Flow Technologies Limited
Priority to AU2002343073A priority Critical patent/AU2002343073A1/en
Publication of WO2003045280A1 publication Critical patent/WO2003045280A1/en

Links

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02Prostheses implantable into the body
    • A61F2/04Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
    • A61F2/06Blood vessels
    • FMECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F15FLUID-PRESSURE ACTUATORS; HYDRAULICS OR PNEUMATICS IN GENERAL
    • F15DFLUID DYNAMICS, i.e. METHODS OR MEANS FOR INFLUENCING THE FLOW OF GASES OR LIQUIDS
    • F15D1/00Influencing flow of fluids
    • F15D1/02Influencing flow of fluids in pipes or conduits
    • F15D1/04Arrangements of guide vanes in pipe elbows or duct bends; Construction of pipe conduit elements or elbows with respect to flow, specially for reducing losses in flow
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
    • A61F2/91Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02Prostheses implantable into the body
    • A61F2/04Hollow or tubular parts of organs, e.g. bladders, tracheae, bronchi or bile ducts
    • A61F2/06Blood vessels
    • A61F2002/068Modifying the blood flow model, e.g. by diffuser or deflector
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2210/00Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2210/0004Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof bioabsorbable
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2220/00Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2220/0008Fixation appliances for connecting prostheses to the body
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2250/00Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0004Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof adjustable
    • A61F2250/0013Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof adjustable for adjusting fluid pressure

Definitions

  • This invention relates to an insert for a conduit, and especially, but not solely, an insert to modify flow in blood flow tubing such as veins and arteries of the human or animal body for the purpose of effecting helical flow therein.
  • WO 00/38591 discloses modified blood flow tubing and stents for use in blood flow tubing with spiral configurations that induce spiral (or helical) flow in the tubing.
  • spiral flow has a beneficial effect in reducing turbulence and dead flow spots in the tubing. It is believed that turbulence and dead flow spots contribute to the build up of plaque, or narrowing of blood vessels, which can result in blockage at or downstream of the tubing or stent.
  • Stents are commonly used to open up and/or maintain open constricted arteries, and, as disclosed in WO 00/38591, can incorporate helical formations to induce the desired spiral flow.
  • stents are already of some complexity, arising from the need to introduce them in compact form for easy passage through the artery to the target site, then to expand them to open the restriction or to fit a previously opened restriction.
  • Introducing a helical flow inducing configuration is an added complication.
  • an insert for a conduit the insert being adapted to effect helical flow in the conduit and comprising a longitudinally extending member defining at least a portion of a helix.
  • the terms "helix”, “helical” and “spiral” as used herein cover the mathematical definition of helix and helical and any combination of the mathematical definitions of helical and spiral.
  • the longitudinally extending member may be, in cross-section, flat. However, it may have an inwardly extending portion that extends inwardly of the helix and also extends lengthwise along the member. The inwardly extending portion may extend along an edge of the longitudinally extending member, or may extend, lengthwise, intermediate the edges of the longitudinally extending member.
  • the longitudinally extending member may have two inwardly extending portions, and preferably, at least one may extend lengthwise along an edge of the longitudinally extending member.
  • the inwardly extending portion, or portions is movable between the inwardly extended position and a collapsed position.
  • the portion(s) can be moved to the collapsed position when the stent is collapsed to facilitate insertion of the stent.
  • the inwardly extending portion, or portions are biased towards the extended position.
  • the biasing of the inwardly extending portions to the extended position is enabled by an elastic deformation of the inwardly extending portion(s) to the collapsed position(s).
  • the inwardly extending portion may be elastically compressible or elastically deflectable to the collapsed position.
  • the longitudinally extending member is adapted to be attached to an internal side wall of a conduit, such as a stent, stent graft or graft.
  • a conduit such as a stent, stent graft or graft.
  • the longitudinally extending member defines a helix or helix/spiral combination around the longitudinal axis of the conduit.
  • the longitudinally extending member may be so configured in relation to a conduit for which it is adapted that its cross-section at any position along the conduit is substantially on a diameter of the conduit cross- section.
  • the insert may be adapted to lodge inside a vein or artery of the human or animal body, and may be adapted to lodge inside a stent in a vein or artery of the human or animal body, or a graft therein.
  • the insert may have a pitch, in relation to its length, such that one end is angularly displaced from the other by less than one revolution.
  • the revolution of the total length of the insert is at least 50%, and preferably at least 70% of one revolution. If multiple inserts are provided in the conduit, the revolution may be the combined total of the revolution of each insert.
  • the insert comprises a biocompatible material, if it is to be left for any length of time.
  • the insert may also be biodegradable, so that it can serve for a predetermined period of time without needing to be removed.
  • a stent comprising a tubular body member and an insert mounted within the body member, the insert comprising a longitudinally extending member defining at least a portion of a helix.
  • the tubular body member is movable between a collapsed position, during insertion of the stent, and an expanded position, when the stent is located in the desired position.
  • the longitudinally extending member has an inwardly extending portion that extends inwardly away from the internal side-wails of the tubular body section.
  • the inwardly extending portion is movable to a collapsed position.
  • the stent comprises a single insert.
  • the stent may comprise two or more inserts, typically, on the same cross-section of the tubular body member.
  • the portion of a helix defined by the longitudinally extending member is at least 50% of one revolution, and preferably at least 70% of one revolution.
  • the total portion of a helix defined by all the longitudinally extending members may be at least 50%, and preferably, at least 70% of one revolution.
  • the insert has two inwardly extending portions extending along the length of the longitudinally extending member.
  • the insert may have only one inwardly extending portion extending along the length of the longitudinally extending member.
  • Figure 1 is a side view of a stent with a first insert
  • Figure 2 is an end view of the stent of Figure 1 ;
  • Figure 3 is a cross-section view of the first insert in an open position
  • Figure 4 is a cross-section view of the first insert in a collapsed position
  • Figure 5 is a cross-section al view of a second insert
  • Figure 6 is a cross-sectional view of a third insert
  • Figure 7 is a cross-sectional view of a fourth insert in an extended position
  • Figure 8 is a cross-sectional view of the fourth insert in a collapsed position
  • Figure 9 is a schematic diagram showing relative positions of a cuff and a stent in a carotid artery of a pig;
  • Figure 10 is a section along the line CC of Figure 9 of a right carotid artery fitted with a prior art stent;
  • Figure 11 is a section along the line CC of Figure 9 of a left carotid artery of a pig fitted with the stent shown in Figures 1 and 2.
  • Figures 1 and 2 show a stent 1 having a main body 4 which is formed from a wire mesh material.
  • the stent 1 could be formed from a tube with interruptions or a laser cut tube providing an expandable homogeneous structure.
  • Attached to the internal side wall of the body 4 is an insert 2 which defines a helix.
  • the insert 2 is typically manufactured from a biocompatible material, such as polyurethane, and may be attached to the internal side wall of the body 4 by injection moulding, insert moulding, glue or melting base portion 5 of the insert 2 onto the body 4 such that after cooling, the mesh structure of the body 4 is entrained with the base portion 5 of the insert 2.
  • insert 2 also includes two fins 6, 7 extending from the base portion 5 at opposite edges of the base portion 5. It will be noted from Figures 1 and 2 that the fins 6, 7 extend along the length of the insert 2 and extend inwardly from the internal side walls of the main body 4.
  • the stent 1 is inserted into a blood vessel in the human or animal body in a collapsed configuration and after it is located in the correct position, it is expanded to engage with the side walls of the blood vessel to locate the stent 1 in the desired position.
  • the stent 1 is inserted on a balloon catheter with the stent 1 in the collapsed configuration around the collapsed balloon of the catheter.
  • the balloon is then inflated by pumping fluid into the balloon through the catheter.
  • the expansion of the balloon expands the stent 1 into engagement with the internal side walls of the blood vessel.
  • the configuration of the stent 1 shown in Figure 1 is in the expanded position. That is, the configuration after it is engaged with the internal side walls of the vessels by expanding the balloon of a balloon catheter, and the balloon catheter is removed.
  • the stent 1 may be formed from an expansible material that "self- expands" into position, for example, by thermal mending properties.
  • the insert 2 When the stent 1 is collapsed onto the balloon of the catheter, or the stent delivery system, the insert 2 is designed such that the fins 6, 7 are bent inwardly so that the fins of the insert collapse so as to reduce the volume occupied by the insert 2 when the stent 1 is in the collapsed configuration.
  • This is illustrated in Figure 4 where it can be seen that fin 7 bends inwardly to overlie the base 5 and fin 6 bends inwardly to overlie the fin 7.
  • This feature is enabled by appropriate design of the base portion 5 and fins 6, 7 and a suitable choice of material for the insert 2.
  • this is an elastically deformable material, such as a suitable plastic material, for example, polyurethane.
  • the fins 6, 7 automatically return to the non-collapsed position, shown in Figure 2, after expansion of the stent 1 and removal of the balloon catheter.
  • the insert 2 After insertion and placement in the desired blood vessel, the insert 2, due to its helical shape, acts on blood flowing through the stent 1 to generate a spiral flow component in the blood.
  • the length of the stent 1 is to a large extent dictated by enabling sufficient flexibility to ensure that the stent 1 can be inserted into the desired location in the human or animal body or the length of the narrowed artery requiring or able to be supported by the stent. That is, the length may depend on the length of the vessel needing treatment. Accordingly, the stent 1 typically has a length in the region of 10 mm to 100 mm. For certain vessels this may be normally approximately 20 mm to 40 mm in length. In order for the insert 2 to generate spiral flow of blood passing through the stent 1 , the helix angle of the helix defined by the insert 2 must not be too high.
  • the insert 2 typically defines only a portion of one revolution of the helix that it defines. Preferably, this is at least 50% of one revolution and most preferably greater than 70% of one revolution. However, the effect may be enhanced by using a number of inserts 2 within the stent 1.
  • a pig had the stent 1 inserted, on a balloon catheter delivery system, in the left carotid artery and a cuff applied surgically to the artery downstream of the stent.
  • a prior art stent identical to the stent 1 , except for the absence of the insert 2 was inserted in a similar manner in the right carotid artery and a cuff was also applied surgically to the right carotid artery downstream of the prior art stent.
  • the stent placements and the downstream cuffs were checked by intra-arterial contrast injection under X-ray (angiography).
  • the cuffs 41 applied a moderate stenosis to each of the right and left carotid arteries 40 downstream of the stent.
  • the cuffs 41 each produced a stenosis of approximately 75%.
  • the relative positions of the stents in the carotid arteries 40 and the cuffs 41 are shown in Figure 9.
  • the left and right carotid arteries 40 were explanted and examined grossly and histologically.
  • the three sites along the carotid arteries 40 which were compared for the right and left carotid arteries 40 are indicated by the lines AA, BB and CC in Figure 9.
  • the intimal and medial thickness and the intimal/medial thickness ratio were determined.
  • the results are shown in Table 1 below and sections at site CC for the right and left carotid arteries are shown in Figures 10 and 11 , respectively.
  • the insert 2 may be attached to a flexible material, such as a membrane, and that the flexible material is then attached to the inside and/or outside of the body 4.
  • the flexible material may be a woven, knitted or spun polyester material, polyurethane material or extended PTFE material, and may be in the form of a tube which locates within the body 4 and is attached to the body 4 by a suitable means, such as adhesive or by stitching.
  • the flexible material may be porous.
  • the stent 1 Although in the stent 1 only one insert 2 is used, it is possible that multiple inserts may be used in either end-to-end and/or side-by-side relationship within the body 4. Where multiple inserts are used, the total portion of the helix defined by all the inserts is typically greater than 50% and preferably greater than 70%. This means that any one insert may define a portion of a helix that is less than 50%.
  • Figure 5 shows a second example of an insert 10 that includes a base portion 11 with a fin 12 extending from one edge of the base portion 11. As with the insert 2, the fin 12 extends along the length of the insert 10.
  • Figure 6 shows a third example of an insert 20 that includes a base portion 21 with a fin 22 extending centrally from the base portion 21. As with the inserts 2, 10 the fin 22 extends along the length of the insert 20.
  • Figures 7 and 8 show a fourth example of an insert 24 that has a fin 23 formed from an elastically compressible foam material 25, such as a polyurethane foam.
  • Figure 7 shows the insert 24 with the fin 23 in the extended position and
  • Figure 8 shows the insert 24 with the foam material 25 compressed so that the fin 23 is collapsed.
  • the inserts 10, 20, 24 may be used in the stent 1 in the same manner as the insert 2.
  • the helical formations 2, 10, 20, 24 may each have a pitch, in relation to their length, such that one end is angularly displaced from the other by at least 50% of one revolution and preferably at least 70% of one revolution. This is found to impart favourable spiral flow to flow in a vein or artery, eliminating, or at least reducing, turbulence and dead spots with reduction of plaque formation.
  • a biocompatible material will be selected, and a smooth structure with rounded ends will be preferred so as not to introduce any turbulence into the flow.

Abstract

There is disclosed an insert (2) for a conduit (4) adapted to effect helical flow in the conduit (4) comprising a longitudinally extending member having a helical formation.

Description

HELICAL INSERT FOR A CONDUIT
This invention relates to an insert for a conduit, and especially, but not solely, an insert to modify flow in blood flow tubing such as veins and arteries of the human or animal body for the purpose of effecting helical flow therein.
WO 00/38591 discloses modified blood flow tubing and stents for use in blood flow tubing with spiral configurations that induce spiral (or helical) flow in the tubing. There is evidence that spiral flow has a beneficial effect in reducing turbulence and dead flow spots in the tubing. It is believed that turbulence and dead flow spots contribute to the build up of plaque, or narrowing of blood vessels, which can result in blockage at or downstream of the tubing or stent.
Stents are commonly used to open up and/or maintain open constricted arteries, and, as disclosed in WO 00/38591, can incorporate helical formations to induce the desired spiral flow.
However, stents are already of some complexity, arising from the need to introduce them in compact form for easy passage through the artery to the target site, then to expand them to open the restriction or to fit a previously opened restriction. Introducing a helical flow inducing configuration is an added complication.
In accordance with a first aspect of the present invention, there is provided an insert for a conduit, the insert being adapted to effect helical flow in the conduit and comprising a longitudinally extending member defining at least a portion of a helix.
The terms "helix", "helical" and "spiral" as used herein cover the mathematical definition of helix and helical and any combination of the mathematical definitions of helical and spiral. The longitudinally extending member may be, in cross-section, flat. However, it may have an inwardly extending portion that extends inwardly of the helix and also extends lengthwise along the member. The inwardly extending portion may extend along an edge of the longitudinally extending member, or may extend, lengthwise, intermediate the edges of the longitudinally extending member.
The longitudinally extending member may have two inwardly extending portions, and preferably, at least one may extend lengthwise along an edge of the longitudinally extending member.
Preferably, the inwardly extending portion, or portions, is movable between the inwardly extended position and a collapsed position. This has the advantage that where the insert is used in a stent, the portion(s) can be moved to the collapsed position when the stent is collapsed to facilitate insertion of the stent. Typically, the inwardly extending portion, or portions, are biased towards the extended position. Hence, when the stent is expanded, the inwardly extending portion(s) move when permitted to the extended position. Preferably, the biasing of the inwardly extending portions to the extended position is enabled by an elastic deformation of the inwardly extending portion(s) to the collapsed position(s). For example, the inwardly extending portion may be elastically compressible or elastically deflectable to the collapsed position.
Typically, the longitudinally extending member is adapted to be attached to an internal side wall of a conduit, such as a stent, stent graft or graft. In this example the longitudinally extending member defines a helix or helix/spiral combination around the longitudinal axis of the conduit.
Alternatively, it is possible that the longitudinally extending member may be so configured in relation to a conduit for which it is adapted that its cross-section at any position along the conduit is substantially on a diameter of the conduit cross- section. The insert may be adapted to lodge inside a vein or artery of the human or animal body, and may be adapted to lodge inside a stent in a vein or artery of the human or animal body, or a graft therein.
The insert may have a pitch, in relation to its length, such that one end is angularly displaced from the other by less than one revolution. Typically, the revolution of the total length of the insert is at least 50%, and preferably at least 70% of one revolution. If multiple inserts are provided in the conduit, the revolution may be the combined total of the revolution of each insert.
Preferably, where the insert is for use in the human or animal body, the insert comprises a biocompatible material, if it is to be left for any length of time.
In one example of the invention, the insert may also be biodegradable, so that it can serve for a predetermined period of time without needing to be removed.
In accordance with a second aspect of the present invention, there is provided a stent comprising a tubular body member and an insert mounted within the body member, the insert comprising a longitudinally extending member defining at least a portion of a helix.
Preferably, the tubular body member is movable between a collapsed position, during insertion of the stent, and an expanded position, when the stent is located in the desired position.
Typically, the longitudinally extending member has an inwardly extending portion that extends inwardly away from the internal side-wails of the tubular body section. Preferably, the inwardly extending portion is movable to a collapsed position.
In one example of the invention, the stent comprises a single insert. However, in other examples of the invention, the stent may comprise two or more inserts, typically, on the same cross-section of the tubular body member. Typically, the portion of a helix defined by the longitudinally extending member is at least 50% of one revolution, and preferably at least 70% of one revolution.
However, if multiple inserts are provided, the total portion of a helix defined by all the longitudinally extending members may be at least 50%, and preferably, at least 70% of one revolution.
Preferably, the insert has two inwardly extending portions extending along the length of the longitudinally extending member. However, alternatively, the insert may have only one inwardly extending portion extending along the length of the longitudinally extending member.
Inserts for a conduit in accordance with the invention will now be described with reference to the accompanying drawings, in which:
Figure 1 is a side view of a stent with a first insert;
Figure 2 is an end view of the stent of Figure 1 ;
Figure 3 is a cross-section view of the first insert in an open position;
Figure 4 is a cross-section view of the first insert in a collapsed position;
Figure 5 is a cross-section al view of a second insert; Figure 6 is a cross-sectional view of a third insert;
Figure 7 is a cross-sectional view of a fourth insert in an extended position;
Figure 8 is a cross-sectional view of the fourth insert in a collapsed position;
Figure 9 is a schematic diagram showing relative positions of a cuff and a stent in a carotid artery of a pig; Figure 10 is a section along the line CC of Figure 9 of a right carotid artery fitted with a prior art stent; and
Figure 11 is a section along the line CC of Figure 9 of a left carotid artery of a pig fitted with the stent shown in Figures 1 and 2.
Figures 1 and 2 show a stent 1 having a main body 4 which is formed from a wire mesh material. Alternatively, the stent 1 could be formed from a tube with interruptions or a laser cut tube providing an expandable homogeneous structure. Attached to the internal side wall of the body 4 is an insert 2 which defines a helix. The insert 2 is typically manufactured from a biocompatible material, such as polyurethane, and may be attached to the internal side wall of the body 4 by injection moulding, insert moulding, glue or melting base portion 5 of the insert 2 onto the body 4 such that after cooling, the mesh structure of the body 4 is entrained with the base portion 5 of the insert 2.
A cross-sectional view of the insert 2 is shown in Figure 3 where it can be seen that insert 2 also includes two fins 6, 7 extending from the base portion 5 at opposite edges of the base portion 5. It will be noted from Figures 1 and 2 that the fins 6, 7 extend along the length of the insert 2 and extend inwardly from the internal side walls of the main body 4.
In use, the stent 1 is inserted into a blood vessel in the human or animal body in a collapsed configuration and after it is located in the correct position, it is expanded to engage with the side walls of the blood vessel to locate the stent 1 in the desired position. Typically, the stent 1 is inserted on a balloon catheter with the stent 1 in the collapsed configuration around the collapsed balloon of the catheter. When the stent 1 is in the correct position in a blood vessel, the balloon is then inflated by pumping fluid into the balloon through the catheter. The expansion of the balloon expands the stent 1 into engagement with the internal side walls of the blood vessel. The configuration of the stent 1 shown in Figure 1 is in the expanded position. That is, the configuration after it is engaged with the internal side walls of the vessels by expanding the balloon of a balloon catheter, and the balloon catheter is removed.
Alternatively, the stent 1 may be formed from an expansible material that "self- expands" into position, for example, by thermal mending properties.
When the stent 1 is collapsed onto the balloon of the catheter, or the stent delivery system, the insert 2 is designed such that the fins 6, 7 are bent inwardly so that the fins of the insert collapse so as to reduce the volume occupied by the insert 2 when the stent 1 is in the collapsed configuration. This is illustrated in Figure 4 where it can be seen that fin 7 bends inwardly to overlie the base 5 and fin 6 bends inwardly to overlie the fin 7. This feature is enabled by appropriate design of the base portion 5 and fins 6, 7 and a suitable choice of material for the insert 2. Typically, this is an elastically deformable material, such as a suitable plastic material, for example, polyurethane. Hence, as the collapsing is an elastic deformation of the insert 2, the fins 6, 7 automatically return to the non-collapsed position, shown in Figure 2, after expansion of the stent 1 and removal of the balloon catheter.
After insertion and placement in the desired blood vessel, the insert 2, due to its helical shape, acts on blood flowing through the stent 1 to generate a spiral flow component in the blood.
The length of the stent 1 is to a large extent dictated by enabling sufficient flexibility to ensure that the stent 1 can be inserted into the desired location in the human or animal body or the length of the narrowed artery requiring or able to be supported by the stent. That is, the length may depend on the length of the vessel needing treatment. Accordingly, the stent 1 typically has a length in the region of 10 mm to 100 mm. For certain vessels this may be normally approximately 20 mm to 40 mm in length. In order for the insert 2 to generate spiral flow of blood passing through the stent 1 , the helix angle of the helix defined by the insert 2 must not be too high. Therefore, to generate an effective spiral flow component, the insert 2 typically defines only a portion of one revolution of the helix that it defines. Preferably, this is at least 50% of one revolution and most preferably greater than 70% of one revolution. However, the effect may be enhanced by using a number of inserts 2 within the stent 1.
When blood flows through the stent 1, the helical formation of the insert 2 will tend to generate a spiral flow formation in the blood exiting from the stent 1. This spiral flow tends to reduce turbulence and promote better flow of blood within the blood vessels of the human or animal body into which it is inserted.
This has been supported by experimental results. A pig had the stent 1 inserted, on a balloon catheter delivery system, in the left carotid artery and a cuff applied surgically to the artery downstream of the stent. A prior art stent identical to the stent 1 , except for the absence of the insert 2, was inserted in a similar manner in the right carotid artery and a cuff was also applied surgically to the right carotid artery downstream of the prior art stent. The stent placements and the downstream cuffs were checked by intra-arterial contrast injection under X-ray (angiography). The cuffs 41 applied a moderate stenosis to each of the right and left carotid arteries 40 downstream of the stent. The cuffs 41 each produced a stenosis of approximately 75%. The relative positions of the stents in the carotid arteries 40 and the cuffs 41 are shown in Figure 9.
After two weeks the left and right carotid arteries 40 were explanted and examined grossly and histologically. The three sites along the carotid arteries 40 which were compared for the right and left carotid arteries 40 are indicated by the lines AA, BB and CC in Figure 9. At each site AA, BB, CC the intimal and medial thickness and the intimal/medial thickness ratio were determined. The results are shown in Table 1 below and sections at site CC for the right and left carotid arteries are shown in Figures 10 and 11 , respectively.
Figure imgf000009_0001
Table 1
A comparison of Figures 10 and 11 shows that there was extensive intimal thickening in the distal cuff of the right carotid artery (i.e. the artery with the prior art stent) but little intimal thickening in the distal cuff of the left carotid artery (i.e. the artery with the stent 1 ). This is supported quantitatively by Table 1 , which shows that intimal/medial thickness ratio at location CC was 89.7% for the right carotid artery, but only 2.7% for the left carotid artery. In addition, it can be seen from Figure 10 that there was also loss of lumen of the right artery at site CC. While Figure 11 shows that there was no loss of lumen of the left artery at site CC.
As an alternative to attaching the insert 2 directly to the body 4, it is also possible that the insert 2 may be attached to a flexible material, such as a membrane, and that the flexible material is then attached to the inside and/or outside of the body 4. For example, the flexible material may be a woven, knitted or spun polyester material, polyurethane material or extended PTFE material, and may be in the form of a tube which locates within the body 4 and is attached to the body 4 by a suitable means, such as adhesive or by stitching. The flexible material may be porous.
Although in the stent 1 only one insert 2 is used, it is possible that multiple inserts may be used in either end-to-end and/or side-by-side relationship within the body 4. Where multiple inserts are used, the total portion of the helix defined by all the inserts is typically greater than 50% and preferably greater than 70%. This means that any one insert may define a portion of a helix that is less than 50%.
Figure 5 shows a second example of an insert 10 that includes a base portion 11 with a fin 12 extending from one edge of the base portion 11. As with the insert 2, the fin 12 extends along the length of the insert 10.
Figure 6 shows a third example of an insert 20 that includes a base portion 21 with a fin 22 extending centrally from the base portion 21. As with the inserts 2, 10 the fin 22 extends along the length of the insert 20.
Figures 7 and 8 show a fourth example of an insert 24 that has a fin 23 formed from an elastically compressible foam material 25, such as a polyurethane foam. Figure 7 shows the insert 24 with the fin 23 in the extended position and Figure 8 shows the insert 24 with the foam material 25 compressed so that the fin 23 is collapsed. The inserts 10, 20, 24 may be used in the stent 1 in the same manner as the insert 2.
The helical formations 2, 10, 20, 24 may each have a pitch, in relation to their length, such that one end is angularly displaced from the other by at least 50% of one revolution and preferably at least 70% of one revolution. This is found to impart favourable spiral flow to flow in a vein or artery, eliminating, or at least reducing, turbulence and dead spots with reduction of plaque formation.
For helical formations 2, 10, 20, 24 intended to remain on more than just a temporary basis, a biocompatible material will be selected, and a smooth structure with rounded ends will be preferred so as not to introduce any turbulence into the flow.
The use of stents as described is clearly not restricted to blood flow tubing. Other tubing - including external blood flow, eg. dialysis and heart-lung machine tubing, as well as tubing and pipework in industrial and civil engineering could also benefit from inserts, as described herein, and the invention, whilst it has been specifically described and illustrated with reference to blood flow tubing is to be regarded as of more general application.

Claims

1. An insert for a conduit the insert being adapted to effect helical flow in the conduit and comprising a longitudinally extending member defining at least a portion of a helix.
2. An insert according to claim 1 , wherein the longitudinally extending member has an inwardly extending portion that extends inwardly of the helix and also extends lengthwise along the member.
3. An insert according to claim 2, wherein the inwardly extending portion extends along an edge of the longitudinally extending member.
4. An insert according to claim 2 or claim 3, wherein the longitudinally extending member comprises two inwardly extending portions, of which at least one extends along an edge of the longitudinally extending member.
5. An insert according to claim 2, wherein the inwardly extending portion extends lengthwise and intermediate the edges of the longitudinally extending member.
6. An insert according to any of claims 1 to 5, wherein the insert is adapted to lodge inside a vein or artery of the human or animal body, or a graft therein.
7. An insert according to any of claims 1 to 5, wherein the insert is adapted to lodge inside a stent in a vein or artery of the human or animal body, or a graft therein.
8. An insert according to any of the preceding claims, wherein the rotation of a helix is at least 50% of one revolution.
9. An insert according to claim 8, wherein the rotation of the helix is at least 70% of one revolution.
10. An insert according to any one of claims 1 to 9, wherein the insert is manufactured from a material comprising a biocompatible material.
11. An insert according to any once of claims 1 to 10, wherein the insert is manufactured from a material comprising a biodegradable material.
12. A stent comprising a tubular body section and an insert mounted within the body section, the insert comprising a longitudinally extending member defining at least a portion of a helix.
13. A stent according to claim 12, wherein the longitudinally extending member has an inwardly extending portion that extends inwardly away from the internal side-walls of the tubular body section.
14. A stent according to claim 13, wherein the inwardly extending portion is movable between the extended position and a collapsed position.
15. A stent according to claim 14, wherein the longitudinally extending member comprises an elastically compressible material.
16. A stent according to any of claims 12 to 15, wherein the insert has two inwardly extending portions extending along the length of the longitudinally extending member.
17. A stent according to any of claims 12 to 16, wherein the portion of a helix defined by the longitudinally extending member is at least 50% of one revolution.
18. The stent according to claim 17, wherein the portion of the helix is at least 70% of one revolution.
19. A stent according to any of claims 12 to 18, wherein the insert is mounted within a flexible tubular material and the flexible tubular material is mounted on the body section.
PCT/GB2002/005276 2001-11-21 2002-11-21 Helical insert for a conduit WO2003045280A1 (en)

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Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2005077305A1 (en) 2004-02-06 2005-08-25 Tayside Flow Technologies Ltd A drug delivery device
US8133277B2 (en) 2004-10-21 2012-03-13 Bard Peripheral Vascular, Inc. Medical device for fluid flow and method of forming such device

Families Citing this family (32)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20040267349A1 (en) 2003-06-27 2004-12-30 Kobi Richter Amorphous metal alloy medical devices
US8382821B2 (en) 1998-12-03 2013-02-26 Medinol Ltd. Helical hybrid stent
GB9828696D0 (en) 1998-12-29 1999-02-17 Houston J G Blood-flow tubing
CN1172299C (en) 1999-10-30 2004-10-20 三星电子株式会社 Optical probe
US7390331B2 (en) 2001-05-22 2008-06-24 Sanostec Corp Nasal inserts
US8403954B2 (en) 2001-05-22 2013-03-26 Sanostec Corp. Nasal congestion, obstruction relief, and drug delivery
GB2369797B (en) 2001-11-20 2002-11-06 Tayside Flow Technologies Ltd Helical formations in tubes
GB2382776A (en) 2001-11-21 2003-06-11 Tayside Flow Technologies Ltd Helix shaped insert for flow modification in a duct or stent
GB0227369D0 (en) * 2002-11-23 2002-12-31 Tayside Flow Technologies Ltd A helical formation for a conduit
US9039755B2 (en) * 2003-06-27 2015-05-26 Medinol Ltd. Helical hybrid stent
US9155639B2 (en) * 2009-04-22 2015-10-13 Medinol Ltd. Helical hybrid stent
GB0315714D0 (en) * 2003-07-04 2003-08-13 Tayside Flow Technologies Ltd An internal formation for a conduit
US8808354B2 (en) 2004-09-22 2014-08-19 Veryan Medical Limited Helical stent
GB2418362C (en) * 2004-09-22 2010-05-05 Veryan Medical Ltd Stent
US20060085065A1 (en) * 2004-10-15 2006-04-20 Krause Arthur A Stent with auxiliary treatment structure
US7988723B2 (en) 2007-08-02 2011-08-02 Flexible Stenting Solutions, Inc. Flexible stent
US8376053B2 (en) * 2007-10-01 2013-02-19 Premium Artificial Lift Systems Ltd. Fluid flow conduit, method and use
CN101854975A (en) 2007-10-03 2010-10-06 桑诺斯泰克公司 Nasal inserts
US8398705B2 (en) * 2008-06-11 2013-03-19 Eric Mangiardi Stent
US9149376B2 (en) 2008-10-06 2015-10-06 Cordis Corporation Reconstrainable stent delivery system
DE102008050618B3 (en) * 2008-10-09 2010-04-01 Roland Kuffer Device for absorbing electromagnetic radiation
US20100298924A1 (en) * 2009-05-19 2010-11-25 Tayside Flow Technologies Ltd. Vascular Graft
DE102009024960A1 (en) * 2009-06-12 2010-12-16 Dietrich Wetzel Kg Self-cleaning and / or conveying device and / or pressure and / or friction loss-influencing structure
US9095420B2 (en) * 2011-01-24 2015-08-04 Tufts Medical Center, Inc. Endovascular stent
GB2498581A (en) * 2012-01-23 2013-07-24 Rolls Royce Plc Pipe inspection probing cable having an external helical track
GB2514135B (en) 2013-05-14 2015-04-15 Cook Medical Technologies Llc Implantable flow diverter
GB2519932B (en) 2013-08-13 2015-10-21 Cook Medical Technologies Llc Implantable flow adjuster
US9561320B2 (en) 2014-06-05 2017-02-07 Cook Medical Technologies Llc Device for promoting fistula patency and method
EP2952142B1 (en) 2014-06-06 2017-09-06 Cook Medical Technologies LLC Device for forming fistula between blood vessels
US10022252B2 (en) 2015-06-10 2018-07-17 Cook Medical Technologies Llc Spiral blood flow device with diameter independent helix angle
US11491002B2 (en) * 2015-08-14 2022-11-08 Indian Institute Of Technology Bombay Implantable cardio-vascular flow streamliner
CN110645237B (en) * 2019-09-02 2022-01-14 厦门理工学院 Pipeline guiding device

Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE597472C (en) * 1936-01-18 Arthur Kuhlmann Spiral built into pipes as a guide surface
DE2510169A1 (en) * 1975-03-08 1976-09-16 Albert Ziegler Kg Fluid hose or pipe - has projecting strip part on inner wall of line coiling around itself
EP0077130A1 (en) * 1981-10-13 1983-04-20 Mihama Manufacturing Co., Ltd. Turbulence inducing members
US5776160A (en) * 1994-02-02 1998-07-07 Pankaj Pasricha Winged biliary stent
WO2000038591A2 (en) 1998-12-29 2000-07-06 Tayside University Hospitals Nhs Trust Blood-flow tubing

Family Cites Families (46)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US606311A (en) * 1898-06-28 sydenham
US2831662A (en) * 1953-09-14 1958-04-22 Century Electric Company Fluid cooled dynamo electric machine
US4161966A (en) * 1975-10-23 1979-07-24 Kabel-Und Metallwerke Gutehoffnungshutte Aktiengesellschaft Spacer for coaxial tube systems
NL8220336A (en) * 1981-09-16 1984-01-02 Wallsten Hans Ivar Device for dilating vascular tissue - comprises helical spring element which is expanded by relatively rotating ends using external knobs
US4420019A (en) * 1982-04-05 1983-12-13 Dillon Joseph C Flexible, non-kinkable hose and method for making the same
NL8403279A (en) * 1984-10-30 1986-05-16 Philips Nv Laminar-flow heat exchanger with two coaxial metal tubes - with cold liq. in inner tube contg. twisted strip and hot liq. in outer tube contg. helical strip
US4629458A (en) 1985-02-26 1986-12-16 Cordis Corporation Reinforcing structure for cardiovascular graft
US4596548A (en) * 1985-03-25 1986-06-24 Dlp Inc. Single stage venous catheter
SE450809B (en) * 1985-04-10 1987-08-03 Medinvent Sa PLANT TOPIC PROVIDED FOR MANUFACTURING A SPIRAL SPRING SUITABLE FOR TRANSLUMINAL IMPLANTATION AND MANUFACTURED SPIRAL SPRINGS
JPS62144738A (en) * 1985-12-20 1987-06-27 Hisao Kojima Liquid mixer
SU1613835A2 (en) * 1987-11-02 1990-12-15 Предприятие П/Я Г-4371 Heat-exchange tube
WO1990000498A1 (en) * 1988-07-05 1990-01-25 J.M. Voith Gmbh Arrangement for removing coils severed from the binding surrounding a bale
FI85223C (en) * 1988-11-10 1992-03-25 Biocon Oy BIODEGRADERANDE SURGICAL IMPLANT OCH MEDEL.
JPH062726Y2 (en) * 1989-06-23 1994-01-26 住友軽金属工業株式会社 Mist recovery device with twisted plate insertion tube
FR2655548A1 (en) 1989-12-11 1991-06-14 Cleef Jean Francois Van Catheter with walls which are not smooth (catheter with walls which are moulded)
FR2665237B1 (en) * 1990-07-27 1992-11-13 Coflexip FLEXIBLE TUBULAR CARCASS AND CONDUIT COMPRISING SUCH A CARCASS.
US5282847A (en) * 1991-02-28 1994-02-01 Medtronic, Inc. Prosthetic vascular grafts with a pleated structure
US5129910A (en) * 1991-07-26 1992-07-14 The Regents Of The University Of California Stone expulsion stent
US5500013A (en) * 1991-10-04 1996-03-19 Scimed Life Systems, Inc. Biodegradable drug delivery vascular stent
JP3120163B2 (en) * 1992-07-22 2000-12-25 金尾 茂樹 Conductive wire interior cleaner hose
FR2708327B1 (en) 1993-07-01 1995-10-13 Hutchinson Tubular profile, for use as a seal, muffler or flexible conduit for motor vehicles.
JPH09501583A (en) * 1993-08-18 1997-02-18 ダブリュ.エル.ゴア アンド アソシエイツ,インコーポレイティド Tubular endoluminal implant
US6190402B1 (en) 1996-06-21 2001-02-20 Musc Foundation For Research Development Insitu formable and self-forming intravascular flow modifier (IFM) and IFM assembly for deployment of same
US5992465A (en) * 1996-08-02 1999-11-30 Jansen; Robert C. Flow system for pipes, pipe fittings, ducts and ducting elements
ZA9710342B (en) * 1996-11-25 1998-06-10 Alza Corp Directional drug delivery stent and method of use.
US5954104A (en) 1997-02-28 1999-09-21 Abbott Laboratories Container cap assembly having an enclosed penetrator
CH691846A5 (en) * 1997-06-20 2001-11-15 Ecole Polytech intravascular implant expansion deflector.
DE69732229T2 (en) * 1997-07-17 2005-12-29 Schneider (Europe) Gmbh Stent and manufacturing process for it
US6161399A (en) * 1997-10-24 2000-12-19 Iowa-India Investments Company Limited Process for manufacturing a wire reinforced monolayer fabric stent
US6156062A (en) * 1997-12-03 2000-12-05 Ave Connaught Helically wrapped interlocking stent
US6063111A (en) * 1998-03-31 2000-05-16 Cordis Corporation Stent aneurysm treatment system and method
US6019779A (en) * 1998-10-09 2000-02-01 Intratherapeutics Inc. Multi-filar coil medical stent
US6248122B1 (en) * 1999-02-26 2001-06-19 Vascular Architects, Inc. Catheter with controlled release endoluminal prosthesis
US20030225453A1 (en) 1999-03-03 2003-12-04 Trivascular, Inc. Inflatable intraluminal graft
US6364904B1 (en) * 1999-07-02 2002-04-02 Scimed Life Systems, Inc. Helically formed stent/graft assembly
US6340364B2 (en) * 1999-10-22 2002-01-22 Nozomu Kanesaka Vascular filtering device
US20010053931A1 (en) * 1999-11-24 2001-12-20 Salvatore J. Abbruzzese Thin-layered, endovascular silk-covered stent device and method of manufacture thereof
DE10003619B4 (en) * 2000-01-28 2005-09-08 Rexroth Star Gmbh nut unit
EP1294311B1 (en) 2000-05-19 2006-01-04 CONMED Endoscopic Technologies, Inc. Biliary stent and method of making it
US6645221B1 (en) * 2000-05-30 2003-11-11 Zuli, Holdings Ltd. Active arterial embolization filter
US6675901B2 (en) * 2000-06-01 2004-01-13 Schlumberger Technology Corp. Use of helically wound tubular structure in the downhole environment
US6572648B1 (en) * 2000-06-30 2003-06-03 Vascular Architects, Inc. Endoluminal prosthesis and tissue separation condition treatment method
US6416540B1 (en) * 2000-11-01 2002-07-09 Sandip V. Mathur Magnetically actuated cleanable stent and method
GB2379996B (en) * 2001-06-05 2004-05-19 Tayside Flow Technologies Ltd Flow means
GB2382776A (en) 2001-11-21 2003-06-11 Tayside Flow Technologies Ltd Helix shaped insert for flow modification in a duct or stent
GB0227369D0 (en) * 2002-11-23 2002-12-31 Tayside Flow Technologies Ltd A helical formation for a conduit

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE597472C (en) * 1936-01-18 Arthur Kuhlmann Spiral built into pipes as a guide surface
DE2510169A1 (en) * 1975-03-08 1976-09-16 Albert Ziegler Kg Fluid hose or pipe - has projecting strip part on inner wall of line coiling around itself
EP0077130A1 (en) * 1981-10-13 1983-04-20 Mihama Manufacturing Co., Ltd. Turbulence inducing members
US5776160A (en) * 1994-02-02 1998-07-07 Pankaj Pasricha Winged biliary stent
WO2000038591A2 (en) 1998-12-29 2000-07-06 Tayside University Hospitals Nhs Trust Blood-flow tubing

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2005077305A1 (en) 2004-02-06 2005-08-25 Tayside Flow Technologies Ltd A drug delivery device
US8133277B2 (en) 2004-10-21 2012-03-13 Bard Peripheral Vascular, Inc. Medical device for fluid flow and method of forming such device

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US20030139807A1 (en) 2003-07-24
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US20050061380A1 (en) 2005-03-24
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US20080114448A1 (en) 2008-05-15
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US7331989B2 (en) 2008-02-19
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US8021415B2 (en) 2011-09-20
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ATE366560T1 (en) 2007-08-15
ATE424158T1 (en) 2009-03-15
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AU2002343073A1 (en) 2003-06-10
DK1446073T3 (en) 2009-06-22

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