EP0797463A4 - Sonde prenant la forme d'un extenseur in situ - Google Patents

Sonde prenant la forme d'un extenseur in situ

Info

Publication number
EP0797463A4
EP0797463A4 EP95906017A EP95906017A EP0797463A4 EP 0797463 A4 EP0797463 A4 EP 0797463A4 EP 95906017 A EP95906017 A EP 95906017A EP 95906017 A EP95906017 A EP 95906017A EP 0797463 A4 EP0797463 A4 EP 0797463A4
Authority
EP
European Patent Office
Prior art keywords
balloon
stent
tubular member
forming material
fluid
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.)
Withdrawn
Application number
EP95906017A
Other languages
German (de)
English (en)
Other versions
EP0797463A1 (fr
Inventor
Hans A Mische
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Boston Scientific Scimed Inc
Original Assignee
Scimed Life Systems Inc
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 Scimed Life Systems Inc filed Critical Scimed Life Systems Inc
Publication of EP0797463A1 publication Critical patent/EP0797463A1/fr
Publication of EP0797463A4 publication Critical patent/EP0797463A4/fr
Withdrawn legal-status Critical Current

Links

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS 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
    • A61F2/00—Filters 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
    • A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS 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
    • A61F2/00—Filters 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
    • A61F2/95—Instruments specially adapted for placement or removal of stents or stent-grafts
    • A61F2/958—Inflatable balloons for placing stents or stent-grafts
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M25/00—Catheters; Hollow probes
    • A61M25/10—Balloon catheters
    • A61M25/1002—Balloon catheters characterised by balloon shape
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS 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
    • A61F2/00—Filters 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
    • A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/94—Stents retaining their form, i.e. not being deformable, after placement in the predetermined place
    • A61F2/945—Stents retaining their form, i.e. not being deformable, after placement in the predetermined place hardenable, e.g. stents formed in situ
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS 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
    • A61F2/00—Filters 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
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2002/30001—Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
    • A61F2002/30003—Material related properties of the prosthesis or of a coating on the prosthesis
    • A61F2002/3006—Properties of materials and coating materials
    • A61F2002/30062—(bio)absorbable, biodegradable, bioerodable, (bio)resorbable, resorptive
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS 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
    • A61F2/00—Filters 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
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2002/30001—Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
    • A61F2002/30316—The prosthesis having different structural features at different locations within the same prosthesis; Connections between prosthetic parts; Special structural features of bone or joint prostheses not otherwise provided for
    • A61F2002/30535—Special structural features of bone or joint prostheses not otherwise provided for
    • A61F2002/30581—Special structural features of bone or joint prostheses not otherwise provided for having a pocket filled with fluid, e.g. liquid
    • A61F2002/30583—Special structural features of bone or joint prostheses not otherwise provided for having a pocket filled with fluid, e.g. liquid filled with hardenable fluid, e.g. curable in-situ
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS 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
    • A61F2/00—Filters 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
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2002/30001—Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
    • A61F2002/30667—Features concerning an interaction with the environment or a particular use of the prosthesis
    • A61F2002/30672—Features concerning an interaction with the environment or a particular use of the prosthesis temporary
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS 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
    • A61F2/00—Filters 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
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2002/30001—Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
    • A61F2002/30667—Features concerning an interaction with the environment or a particular use of the prosthesis
    • A61F2002/30677—Means for introducing or releasing pharmaceutical products, e.g. antibiotics, into the body
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS 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
    • A61F2210/00—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2210/0004—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof bioabsorbable
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS 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
    • A61F2210/00—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2210/0085—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof hardenable in situ, e.g. epoxy resins
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS 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
    • A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0058—Additional features; Implant or prostheses properties not otherwise provided for
    • A61F2250/0059—Additional features; Implant or prostheses properties not otherwise provided for temporary
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS 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
    • A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2250/0058—Additional features; Implant or prostheses properties not otherwise provided for
    • A61F2250/0067—Means for introducing or releasing pharmaceutical products into the body
    • 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
    • A61M2025/0057—Catheters delivering medicament other than through a conventional lumen, e.g. porous walls or hydrogel coatings
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M25/00—Catheters; Hollow probes
    • A61M25/10—Balloon catheters
    • A61M2025/1043—Balloon catheters with special features or adapted for special applications
    • A61M2025/105—Balloon catheters with special features or adapted for special applications having a balloon suitable for drug delivery, e.g. by using holes for delivery, drug coating or membranes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M25/00—Catheters; Hollow probes
    • A61M25/10—Balloon catheters
    • A61M2025/1043—Balloon catheters with special features or adapted for special applications
    • A61M2025/1052—Balloon catheters with special features or adapted for special applications for temporarily occluding a vessel for isolating a sector

Definitions

  • the present invention relates in general to a device and method for delivering fluid materials to the human vascular system. More particularly, it relates to a novel catheter device and method for delivering drugs and other fluid material to an isolated area of a human vessel.
  • Obstructive atherosclerotic diseases typically result from the build up of fatty substances, known generally as lesions or stenoses, on the interior walls of the human vascular system. These deposits reduce the inside diameter of vessels and thereby restrict blood flow.
  • bypass surgery One commonly used method for treating coronary atherosclerosis is a procedure known as coronary artery bypass graft surgery ("bypass surgery"). Bypass surgery, however, is extremely invasive and poses a high level of risk to the patient. Thus, less invasive and traumatic procedures, such as angioplasty or athercctomy, are usually considered before resorting to bypass surgery.
  • a guiding catheter is introduced at an appropriate location in the human body and routed through the vascular system into the aorta and coronary orifice.
  • a relatively flexible guidewire is advanced through the guiding catheter to the artery, and then steered into side branches (if necessary) to access the lesion.
  • an "over-the-wire" dilatation balloon catheter is passed over the guidewire by inserting the proximal end of the guidewire into the distal end of the balloon catheter and then pushing the balloon catheter over the guidewire until the balloon is adjacent the lesion.
  • the balloon catheter and guide wire are integral and are "loaded” together.
  • the balloon is then inflated by introducing a fluid into the balloon through an inflation lumen in the catheter's shaft.
  • the inflated balloon expands against the blockage to dilate the obstructed blood vessel.
  • the need for a separate guidewire is eliminated by attaching a short flexible guidewire to the distal end of the catheter.
  • Furtlier details of angioplasty procedures and the devices used in such procedures are found in U.S. patent no. 4,983,278 (Euteneuer), and U.S. patent no. 5 ,032, 113 (Burns) . The entire disclosure of each of these patents is incorporated herein by reference.
  • athcrectomy a miniaturized cutting tool is attached to the end of a small diameter flexible catheter and maneuvered through the patient's vascular system to the lesion. The cutting tool is used to cut and remove the lesion from the vessel wall.
  • Angioplasty and atherectomy procedures do not always achieve lasting results. Following cither of these procedures, the diseased blood vessel may recoil or rcstenosis may occur. Other post-procedure concerns include vasoconstriction, vasospasm, or the possibility of an intimal flap occurring. Also, it may be necessary in some instances to abort or "bail-out" of an angioplasty or atherectomy procedure. In these situations, a device known as a stent may be placed inside the vessel to provide additional support at the desired region. Stents are typically hollow cylindrical devices which have sufficient size and rigidity to maintain the diameter of the vessel, while at the same time allowing body fluid to pass.
  • Restenosis may also be combatted by administering a drug to d e patient.
  • the drug may be administered "systemically," which means that the drug is introduced, either orally or intravenously, into the vascular system and circulated throughout the body.
  • drugs that have been tested in human clinicals include: heparin, calcium channel blockcrs, angiotensin converting enzyme inhibitors, fish oil, and growth peptides.
  • Other agents have not been tried in clinicals, but are of interest. These include: thromboxane synthetase inhibitor, serotonin antagonists, HMGCoA reductase inhibitors, platelet derived growth factors, inflammatory cell factors, platelet aggregation inhibitors, and thrombin inhibitors such as hirudin or its analogs.
  • Perfusion is very important in developing a suitable fluid delivery means. It is necessary that the device be capable of safely delivering the agent over an extended period of time, and therefore, devices which occlude blood flow during delivery may not provide the necessary safety.
  • Current research indicates that the initial restenosis events begin immediately after injury and continue intensely for several hours. Thus, it is desirable for the drug delivery system to be capable of safely delivering drugs for several hours, months, or possibly years, beginning immediately after intervention. This research also points out that the initial restenosis events may create a cascade of subsequent events that ultimately lead to intimal thickening.
  • the present invention provides a new and unique in situ stent forming device which may be inserted into a vessel, such as a blood vessel, for forming a stent inside a vessel wall.
  • the stent is delivered to the desired site in fluid form and allowed to harden.
  • the device includes an elongated tubular member having a proximal end, a distal end and a lumen.
  • An inflatable balloon member is attached at the distal end of the tubular member and placed in fluid communication with the lumen.
  • the outer surface of the balloon member is contoured such that it defines at least two spaced ridge seals. When the balloon is inflated, the spaced ridge seals, and the vessel wall define an isolation zone.
  • At least one infusion port is provided on the balloon surface and in fluid communication with the lumen via the interior of the balloon.
  • At least one fluid injection port is in fluid communication with the lumen at the proximal end of the tubular member.
  • the present invention also encompasses a method of using the in situ stent forming device to deliver drugs to a treatment site in desired concentrations.
  • the present invention provides a prolonged time frame for drug delivery in relatively high concentrations.
  • the device and method of the present invention may be advantageously used to repair problems sometimes associated with angioplasty.
  • Figure 1 illustrates an in situ stent forming catheter embodying the present invention.
  • the catheter is shown deflated inside a body vessel;
  • Figure 2 further illustrates the catlieter shown in Figure 1 wherein the balloon portion of the catheter is inflated;
  • Figure 3 further illustrates the catheter shown in Figure 1 after it has formed a stent inside the vessel;
  • Figure 4 is a longitudinal cross sectional view of the inflated catheter shown in Figures 2;
  • Figure 5 is a cross sectional view of the inflated catheter shown in Figure 4, taken along line 5-5;
  • Figure 6 is a cross sectional view of the inflated catheter shown in Figure 4, taken along line 6-6;
  • Figure 7 is a cross sectional view of the inflated catheter shown in Figure 4, taken along line 7-7;
  • Figure 8 illustrates another in situ stent forming catheter embodying the present invention.
  • the catheter is shown inflated inside a body vessel;
  • Figure 9 is a cross sectional view of the catheter shown in Figure 8, taken along line 9-9;
  • Figure 10 is a cross sectional view of the catheter shown in Figure 8, taken along line 10-10;
  • Figure 11 is a cross sectional view of the catheter shown in Figure 8, taken along line 11-11;
  • Figure 12 illustrates another in situ stent forming catheter embodying the present invention.
  • the catheter is shown inflated inside a body vessel;
  • Figure 13 is a cross sectional view of the catheter shown in Figure 12, taken along line 13-13;
  • Figure 14 is a cross sectional view of the catheter shown in Figure 12, taken along line 14-14;
  • Figure 15 is a cross sectional view of the catheter shown in Figure 12, taken along line 15-15;
  • Figure 16 illustrates another in situ stent forming catheter embodying the present invention.
  • the catheter is shown inflated inside a body vessel;
  • Figure 17 is a cross sectional view of the catheter shown in Figure 16, taken along line 17-17;
  • Figure 18 is a cross sectional view of the catheter shown in Figure 16, taken along line 18-18, and
  • Figure 19 is a cross sectional view of the catheter shown in Figure 16, taken along line 19-19.
  • a catheter generally indicated at 28 embodying the features of the present invention is shown inside a body vessel 26, such as a blood vessel.
  • Catheter 28 includes an inflatable balloon assembly generally indicated at 30 and located at the distal end of the catheter.
  • the balloon assembly 30 when the balloon assembly 30 is inflated inside a human vessel 26, it defines a substantially cylindrical chamber 32 between balloon assembly 30 and the interior vessel wall 26a.
  • Catheter 28 delivers a fluid substance to the cylindrical chamber 32 via an internal passageway or lumen 34 (seen in Fig. 4) which extends through the length of catheter 28 and terminates at a series of openings 64 in balloon assembly 30.
  • the fluid maybe pumped through catheter 28 by a conventional balloon catheter inflation arrangement (not shown).
  • the fluid substance is of a type which hardens under certain body conditions existing external to the catheter.
  • a moisture curing polymeric material such as a cyanoacrylate may be used, the moisture being supplied by the body.
  • a preferred cyanoacrylate is N-butyl-2-cyanoacrylate.
  • materials such as polymethyl acrylate (PMA) and polyaglycolic acid (GA), which are moisture curable when in an appropriate solvent based system (which are well known) may be used.
  • PMA polymethyl acrylate
  • GA polyaglycolic acid
  • the fluid substance is a chosen drug which is delivered only to the portion of the vessel wall isolated by balloon assembly 30 or is incorporated into a stent forming material for release over time from an in situ formed stent.
  • catlieter 28 has a proximal end and a distal end. The distal end makes the initial entry into the vascular system and includes balloon assembly 30. The proximal end is opposite the distal end and may be connected in a conventional manner to an external manifold (not shown). Conventional manifolds typically include a port for inserting a guidewire through the catheter, and another port for injecting fluids into the catheter.
  • a guide wire lumen 42 (seen in Fig. 4) is formed by a substantially cylindrical tube 48 which extends along the length of catheter 28.
  • a second tube 50 encases tube 48 and also extends along the length of catheter 28. Sufficient space is provided between tubes 48 and 50 to create lumen 34 for delivering fluid to balloon assembly 30.
  • balloon assembly 30 is attached at the distal end of the second tube 50 and is thereby placed in fluid communication with lumen 34.
  • Balloon assembly 30 may be secured to second tube 50 by a number of known methods such as brazing, RF welding or by means of an adhesive.
  • the distal end of tube 48 extends completely through balloon assembly 30 thereby providing a pathway through lumen 42 for passing a guidewire 52 through catheter 28.
  • Balloon assembly 30 includes a single balloon element 56 made of flexible material capable of expanding under pressure. Many materials arc known in the art. Balloon element 56 has a particular exterior shape when it is inflated and it is this shape which facilitates the formation of chamber 32 inside vessel 26. The exterior shape of balloon element 56 has three major components—a proximal ridge seal 58, a distal ridge seal 60 spaced from ridge seal 58, and a stent forming area 62 therebetween. When the balloon element is inflated, the proximal and distal ridge seals 58 and 60 press against the interior wall of the vessel.
  • the stent forming area 62 is depressed inward from ridge seals 52 and 54 and thus, this area 62 does not extend to the vessel wall when the balloon element is inflated. Accordingly, ridge seals 58 and 60 and the depressed area 62 therebetween, along with the interior wall of the vessel, combine to define the chamber 32 when balloon element 56 is inflated.
  • Area 62 is made from a flexible yet porous material, for example polyethylene, which has a series of openings or perforations 64. These openings 64 allow fluid in the balloon to pass through only after the fluid has reached a predetermined pressure in the balloon. This predetermined pressure is selected such that the balloon is completely inflated before any fluid escapes through the openings.
  • a polyethylene balloon has openings of about 0.003 inches in diameter would operate at about 2 atmospheres.
  • the openings could be in the form of microslits which open at pressure and operate as valves.
  • porous materials such as polytctrafluorocthylene which inherently include openings or pores may be used.
  • the fluid flow through the openings may be controlled by choosing a fluid having sufficient viscosity such that it will only flow through the openings after a predetermined pressure such as 2 ATM has been attained within the balloon.
  • a balloon with 0.003 inches openings including a fluid of about 5 centipoise viscosity would operate at about 2 atmospheres.
  • the stent forming catheter 28 may be employed alone or in combination with other procedures.
  • catheter 28 may be used to place a stent in a vessel following a PTCA procedure.
  • a guiding catheter is introduced at an appropriate location in the patient and routed through the vascular system into the aorta and coronary orifice.
  • a relatively flexible guidewire is advanced through the guiding catheter to the artery and then steered into side branches, if necessary, to access a selected lesion.
  • an "over-the-wire" dilatation balloon catheter is passed over the guidewire by inserting the proximal end of the guidewire into the distal end of the balloon catheter and then pushing the balloon catheter over the guidewire until the balloon is adjacent the lesion.
  • the balloon is then inflated by introducing a fluid into the balloon through an inflation lumen in the catheter's shaft.
  • the inflated balloon expands against the blockage to dilate the obstructed blood vessel.
  • the balloon is then deflated and withdrawn over the guidewire.
  • the stent forming catheter 28 may then be advanced over the guide wire for example and positioned in the same region in which the dilation was performed.
  • FIG. 1 The general operation of the catheter 28 is illustrated in Figures 1-3.
  • the uninflated catheter 28 has been inserted into the body vessel 26 over guide wire 52.
  • Balloon element 56 is then inflated, as shown in Figure 2, by injecting a fluid through lumen 34.
  • the balloon When the balloon is inflated, the ridge seals 58 and 60 contact the interior vessel wall 26a thereby defining the substantially cylindrical chamber 32.
  • the inflation fluid escapes through openings 64 to fill chamber 32.
  • the inflation fluid is also the stent forming material which will havc a number of desirable properties including the ability to harden when exposed to conditions external to the catheter 28 as already noted.
  • the balloon element is deflated by withdrawing fluid from it through lumen 34.
  • Catlieter 28 is then removed and a substantially cylindrical stent 40 (shown in Figure 3) remains in the vessel, having been formed in situ.
  • the stent forming catheter 28 of the present invention provides a number of advantages.
  • the in situ formed stent 40 is substantially hollow and thus it docs not hinder the flow of blood and other body fluids through vessel 26.
  • Stent 40 may be made from a biodegradable material, such as poly lactic acid (PLA) or polymethyl acrylate (PMA) or polyglycolic acid (PGA) or a cyanoacrylate as described hercinabovc which will break down and pass through the patient's system over time.
  • the stent material may also be provided with a drug which is time-released into the vessel wall and/or blood stream.
  • FIGS 8--11 illustrate another stent forming catheter generally indicated at 28a embodying the present invention.
  • Catheter 28a has many of the same features as catlieter 28 shown in Figures 1-7, and these shared features have been assigned the same reference numerals in these later Figures. The following discussion of catheter 28a will focus primarily on the features unique to this embodiment.
  • Catheter 28a includes a balloon assembly generally indicated at 56a comprising a single inflatable balloon at the distal end of die catheter 28a. When inflated, balloon 56a impinges on the interior vessel wall 26a, as explained in more detail below. Balloon 56a is shown inflated inside vessel 26 in Figures 8, 9, 10 and 11.
  • the in situ stent forming device shown in Figures 8-11 has a proximal and a distal end.
  • the proximal end (not shown) may be connected to a manifold of the type commonly known in the art.
  • a manifold typically has two ports.
  • the first port is a guide wire port in communication with the guide wire lumen 42 and can accommodate the introduction of a guide wire 52.
  • the second port is an inflation/stent port which is in fluid communication with the inflation/stent lumen 34 as will be described in more detail below.
  • the guide wire lumen runs substantially throughout the length of the in situ stent forming device.
  • This lumen is formed by a substantially cylindrical tube 48, which in an exemplary embodiment may be made of polyethylene.
  • the outside diameter of this tube may be 1022 inches for example and the inside diameter of the tube may be .016 inches for example.
  • the tube may be approximately 135 centimeters in length, which is approximately the length of the device without the guide wire, for example.
  • tubing 50 which forms the inflation stent lumen.
  • the tubing 50 also forms the outside skin of the catheter part of the device.
  • This piece of tubing 50 which is also substantially cylindrical, may be made of polyethylene, for example. In an exemplary embodiment, its outside diameter is .039 inches and its inside diameter is .032 inches, for example. Its length is .131 centimeters, for example.
  • Balloon 56a is attached to the tubing 50 through the use of an adhesive or the like as is known in the art.
  • Balloon 56a is in fluid communication with the inflation stent lumen 34 and therefore also in fluid communication with the inflation/stent port. As can be seen when comparing this embodiment with the previously described embodiment, this embodiment is similar except that balloon 56a is different.
  • balloon 56a has a spiral or helical trough 68 which forms a spiral or helical stent forming region 70. As can be appreciated, this will form a substantially spiral/helical stent. Therefore, this balloon member 56a also comprises two major surface areas. The first area is the balloon contact area, which at each end has ridge seals 58 and 6054, but throughout the middle has a spiral shaped vessel contacting region 72.
  • This second major region defines a substantially helical stent forming area 68 for forming a stent.
  • the portion of the balloon within the stent forming area is made of a porous material, for example polyethylene having perforations 64 which only emit fluid when a certain predetermined pressure is obtained within the balloon.
  • the perforations may be always open and the inflation/stent forming fluid may be of a viscosity such that it is only emitted when a high enough pressure is attained within the balloon.
  • the device may be inserted into a body lumen such as an artery 26 over a guide wire 52 in an uninflatcd form (not shown). Then, the device is inflated until the ridge seals 58 and 60 and spiral contacting region 72 come into contact with a vessel wall 26a thereby scaling off a substantially helical area 70 for forming a stent. After the ridge seals and spiral contacting region have come into contact with the vessel wall 26a and the pressure within the balloon is increased, perforations 64 in the stent forming region 70 of the balloon open and release the inflation media, which contains a stent forming material.
  • This stent forming material molds around and into the substantially helical area 68 partitioned off by ridge seals 58, 54 and the spiral contacting region, and then hardens or sets only when outside the balloon. The balloon is then deflated and removed, leaving a substantially helical stent in the artery.
  • the in situ formed stent which is substantially helical, docs not hinder blood flow through the arteries.
  • This stent may be formed of biodegradable materials, such as PLA, which will absorb into the vessel and/or bloodstream over time.
  • This material may also contain a drug for delivery, over time, into the vessel wall and/or bloodstream.
  • This embodiment may be used after a PTCA procedure as described for the previously disclosed embodiment. The procedure, for this embodiment, is substantially the same.
  • another preferred embodiment of the present invention includes a balloon assembly generally indicated at 56b comprising a single inflatable balloon at the distal end of a catheter generally indicated at 28b. When inflated, balloon 56b impinges on the vessel wall 26a, as explained in more detail below.
  • the balloon is depicted in an inflated form inside a vessel.
  • the in situ stent device of this embodiment has a proximal and a distal end.
  • the proximal end may comprise a manifold as known in the art.
  • the manifold typically has two ports; the first port is a guide wire port and is in communication with the guide wire lumen 42 and can accommodate the introduction of a guide wire 52.
  • the second port is an inflation/stent port which is in fluid communication with the inflation/stent lumen 48 which will be described in more detail below.
  • the guide wire lumen runs substantially throughout the length of the in situ stent forming device.
  • This lumen is formed by a substantially cylindrical tube 48, which in an exemplary embodiment may be made of polyethylene.
  • the outside diameter of this tube may be .022 inches and the inside diameter of the tube may be .016 inches for example.
  • the tube is approximately 135 centimeters in length, which is approximately the length of the device without die guide wire, for example.
  • Another piece of tubing 50 which forms the inflation/stent lumen.
  • the tubing 50 also forms the outside skin of the catheter part of the device.
  • This piece of tubing 50 which is also substantially cylindrical, may be made of polyethylene, for example. In an exemplary embodiment, its outside diameter is .039 inches and its inside diameter is .032 inches. Its length is .131 centimeters, for example.
  • Balloon 56b is attached to tubing 50 through the use of an adhesive or the like as is known in the art. Balloon 56b is in fluid communication with the inflation/stent lumen 34 and therefore also in fluid communication with the inflation/stent port.
  • this embodiment is similar except that the balloon 56b is different.
  • the balloon member has two crossed spiral or helical troughs 74 which forms a crossed double helical stent forming region 76. As can be appreciated, this will form a substantially crossed double helical stent. Therefore, this balloon member 56b also comprises two major areas. The first area is the balloon contact area, which at each end has ridge seals 58 and 60, but throughout the middle has diamond shaped vessel contacting regions 78. The second major region is the stent forming region 74 which defines a substantially crossed double helical stent forming trough area for forming a stent.
  • the portion of the balloon within the stent forming area is made of a porous material, for example polyethylene which has perforations 64 which only emit fluid when a certain predetermined pressure is obtained within the balloon.
  • the perforations may be always open and the inflation/stent forming fluid may be of a viscosity such that it is only emitted when a high enough pressure is attained within the balloon.
  • the device may be inserted into a body lumen, such as an artery 26, over a guide wire 52 in an uninflated form (not shown).
  • the device is then inflated until the ridge seals 58 and 60 and diamond-shaped contact regions 78 come into contact with the vessel wall 26a thereby sealing off a substantially crossed double helical area 74 for forming a stent.
  • the perforations 64 in the stent forming regions 74 of the balloon open and release the inflation media, which contains a stent forming material. This material cures or hardens only outside the balloon as already noted.
  • This stent forming material molds around and into the substantially crossed double helical area 74 partitioned off by the ridge seals 58, 60 and the diamond shaped vessel contacting regions, and then hardens.
  • the balloon is dicn deflated and removed, leaving a substantially crossed double helical stent in the artery.
  • the in situ formed stent which is substantially crossed double helical, docs not hinder blood flow through the arteries.
  • This stent may be formed of biodegradable materials, such as PMA which will absorb into the vessel and/or bloodstream over time. These materials may also contain a drug for delivery, over time, into die vessel wall and/or bloodstream.
  • This embodiment may be used after a PTCA procedure as described for the previously disclosed embodiment. The procedure, for this embodiment, is substantially the same.
  • FIG. 16 another preferred embodiment of the present invention includes a balloon assembly 56c comprising a single inflatable balloon at die distal end of the cadieter 28c. When inflated, balloon 56c impinges on the vessel wall 26a, as explained in more detail below.
  • FIGS 16, 17, 18 and 19 the balloon is depicted in an inflated form inside a vessel.
  • the in situ stent device of this embodiment has a proximal and a distal end.
  • the proximal end may comprise a manifold as known in the art.
  • the manifold typically has two ports; the first port is a guide wire port and is in communication with the guide wire lumen 42 and can accommodate the introduction of a guide wire 52.
  • the second port is an inflation/stent port which is in fluid communication with the inflation/stent lumen 34 which will be described in more detail below.
  • the guide wire lumen runs substantially throughout the length of the in situ stent forming device.
  • This lumen is formed by a substantially cylindrical tube 48, which in an exemplary embodiment may be made by polyethylene.
  • the outside diameter of this tube may be .022 inches and the inside diameter of the tube may be .016 inches, for example.
  • the tube is approximately 135 centimeters in length, which is approximately the length of die device without the guide wire, for example.
  • tubing 50 which forms the inflation/stent lumen.
  • the tubing 50 also forms die outside skin of die catheter part of the device.
  • This piece of tubing 50 which is also substantially cylindrical, may be made of polyethylene, for example. In an exemplary embodiment, its outside diameter is .039 inches and its inside diameter is .032 inches. Its length is 131 centimeters, for example.
  • balloon 56c At d e distal end of d e tubing 50 there is attached the balloon 56c. Balloon 56c is attached to the tubing 50 through the use of adhesives or the like as is known in the art.
  • Balloon 56c is in fluid communication with the inflation/stent lumen 42 and therefore also in fluid communication with the inflation stent port.
  • tliis embodiment is similar except that the balloon 56c is different.
  • the balloon has a substantially cylindrical stent forming region 80 widi "bumps" 82 which form a substantially cylindrical stent forming region 64.
  • the bumps 82 will form a substantially cylindrical stent with perforations. Therefore, this balloon member 56c also comprises two major areas. The first area is the balloon contact area, which at each end has ridge seals 58 and 60, but throughout the middle has bumps 82 which contact d e vessel wall 26a.
  • This second major region is d e stent forming region 84 which defines a substantially cylindrical stent forming area with bumps 82 for forming a perforated stent.
  • the portion of the balloon within die stent forming area is made of a porous material, for example polyediylene with perforations 64 which only emit fluid when a certain pressure is obtained within the balloon.
  • the perforations may be always open and the inflation/stent forming fluid may be of a viscosity such that it is only emitted when a high enough pressure is attained within the balloon.
  • the device may be inserted into a body lumen such as an artery 26 over a guide wire 52 in an uninflatcd form (not shown). Then, the device is inflated until the ridge seals and bumps come into contact with a vessel wall 26a thereby sealing off a substantially cylindrical area with perforations 64 for forming a stent. After the ridge seals and bumps have come into contact with the vessel wall 26a and the pressure wid in the balloon is increased, the perforations 64 in the stent forming region 84 of the balloon open and release die inflation media, which contains a stent forming material.
  • This stent forming material molds around and into the substantially cylindrical area with perforations 64 partitioned off by the ridge seals 58, 60 and the bumps, and then hardens or sets.
  • the balloon is then deflated and removed, leaving a substantially cylindrical stent with perforation in the artery.
  • the in situ formed stent which is substantially cylindrical with perforations, does not hinder blood flow through the arteries.
  • This stent may be formed of biodegradable materials, such as PLA, which will absorb into the vessel and/or bloodstream over time. These materials may also contain a drug for delivery, over time, into the vessel wall and/or bloodstream.
  • This embodiment may be used after a PTCA procedure as described for die previously disclosed embodiment. The procedure, for this embodiment, is substantially the same.
  • the presently disclosed embodiments of the invention arc beneficial over die prior art.
  • These devices arc capable of an extremely low profile, because of dieir single balloon construction. Therefore, when deflated, the balloon has an extremely low profile and is able to travel through very narrow regions of a patient's vascular system. This is also extremely useful when, due to vasoconstriction or other types of collapse of the vessel wall after PTCA, or before PTCA, the portion of the artery to which the stent must be delivered is extremely narrowed.
  • this device may be used to deliver stent materials now known, or developed in the future, which are capable of delivering a drug to the vessel wall. The stent that is delivered has many advantages over the prior art.
  • the stent may be biodegradable, and/or biocompatiblc, no strict drug regime will be necessary after implantation, as is commonly required with other prior art stents, especially metal stents.
  • PTCA has been highly successful and a great advance in the fight against obstructive coronary artery disease
  • patients may, in some cases, have some problems.
  • These problems such as the forming of flaps after the PTCA, or vasoconstriction or long term restenosis, can be cured using the present invention.
  • the stent delivered may be used to temporarily hold up flaps until they can heal against die vessel wall. This device may also be used to deliver a drug over a long period of time and prevent restenosis.
  • the stent in biodegradable form slowly dissolves into the patient's body. It is also contemplated mat the device can deliver a permanent stent that is located within the patient's body and is biocompatible. This would also reduce the need for long term drug regime.
  • the stent form may be extremely flexible. This would prevent certain problems with prior art stents, such as dissections of artery. In and around the coronary arteries there is much movement due to the beating of d e heart. Therefore, it is highly desirable to have a flexible, non-rigid stent.
  • the formed stents contemplated by the present invention may be highly flexible due to the disclosed shapes and/or materials and therefore well suited to be placed in coronary arteries unlike prior art rigid stents.
  • the guide wire lumen may be eliminated and a guide wire tip, as is known in the art, may be secured to the end of the balloon. Eliminating d e guide wire lumen reduces the profile of the uninflated balloon, thereby allowing it to be maneuvered d rough even smaller portions of a patient's vascular.

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Abstract

Dans cette invention, une matière fluidique durcissable est expulsée par les perforations (64) du ballonnet (30) d'une sonde à ballonnet (28) pour prendre la forme d'un extenseur (40) in situ dans le procédé ACTP (angioplastie coronarienne transluminale percutanée).
EP95906017A 1994-12-14 1994-12-14 Sonde prenant la forme d'un extenseur in situ Withdrawn EP0797463A4 (fr)

Applications Claiming Priority (1)

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PCT/US1994/014654 WO1996018427A1 (fr) 1994-12-14 1994-12-14 Sonde prenant la forme d'un extenseur in situ

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EP0797463A4 true EP0797463A4 (fr) 1999-01-27

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Families Citing this family (23)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
FR2748212B1 (fr) * 1996-05-06 1998-07-31 Nycomed Lab Sa Catheter destine a la delivrance locale d'une substance therapeutiquement active
US5921954A (en) * 1996-07-10 1999-07-13 Mohr, Jr.; Lawrence G. Treating aneurysms by applying hardening/softening agents to hardenable/softenable substances
NL1003178C2 (nl) * 1996-05-21 1997-11-25 Cordis Europ Buisvormige prothese van uithardbaar materiaal.
FR2753907B1 (fr) * 1996-10-02 1999-07-16 Nycomed Lab Sa Ballon pour catheter de dilatation et son procede de fabrication
NL1005190C2 (nl) * 1997-02-05 1998-08-06 Vesalius N V Samenstel ter behandeling van een aandoening van een lichaamsholte of lichaamsvat.
US6338726B1 (en) * 1997-02-06 2002-01-15 Vidacare, Inc. Treating urinary and other body strictures
EP2072064B1 (fr) 2003-01-02 2019-04-24 de Vries, Alexander Cornelis Composition pour réparation de vaisseau in vivo
EP1435248A1 (fr) 2003-01-02 2004-07-07 Vesalius N.V. Composition pour la réparation vasculaire in vivo
JP4614265B2 (ja) * 2004-05-06 2011-01-19 朝日インテック株式会社 体内観察用カテーテル
EP1669099A1 (fr) 2004-12-09 2006-06-14 Acrostak Corp. Ensemble de cathéter pour le traitement de vaisseaux sanguins avec médicaments
EP2254530B1 (fr) * 2008-02-25 2013-12-11 Mayo Foundation for Medical Education and Research Endoprothèses conformables
US8187221B2 (en) * 2008-07-11 2012-05-29 Nexeon Medsystems, Inc. Nanotube-reinforced balloons for delivering therapeutic agents within or beyond the wall of blood vessels, and methods of making and using same
JP5337478B2 (ja) * 2008-12-26 2013-11-06 富士フイルム株式会社 鼻腔拡張用補助具
IT1399809B1 (it) * 2009-07-20 2013-05-03 Cid S R L Palloncino per cateteri e relativo procedimento di produzione
ES2549000T3 (es) 2009-07-27 2015-10-22 Endologix, Inc. Endoprótesis
US9005163B2 (en) 2010-08-03 2015-04-14 Bayer Pharma Aktiengesellschaft Balloon catheter with external delivery tube
GB2484952B (en) * 2010-10-27 2012-09-26 Cook Medical Technologies Llc Valvuloplasty balloon catheter
JP2015128457A (ja) * 2012-04-27 2015-07-16 テルモ株式会社 塞栓物吐出カテーテル
US10537375B2 (en) 2015-04-24 2020-01-21 Neurotronic, Inc. Chemical ablation and method of treatment for various diseases
WO2014070820A2 (fr) 2012-11-02 2014-05-08 Lixiao Wang Formulations d'ablation chimique et méthodes de traitement de diverses maladies
JP2017533036A (ja) * 2014-10-30 2017-11-09 ニューロトロニック・インコーポレイテッドＮｅｕｒｏｔｒｏｎｉｃ， Ｉｎｃ． 様々な疾患のための処置の化学的アブレーションおよび方法
US10588503B2 (en) 2016-03-29 2020-03-17 Terumo Kabushiki Kaisha Methods and medical elongate bodies
JP6704277B2 (ja) * 2016-03-29 2020-06-03 テルモ株式会社 医療用長尺体

Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1995008289A2 (fr) * 1993-09-16 1995-03-30 Scimed Life Systems, Inc. Reparation percutanee d'anomalies cardio-vasculaires et compositions associees

Family Cites Families (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4876906A (en) 1986-11-20 1989-10-31 Sundstrand Corporation Non-jamming actuator system
US4983278A (en) 1987-11-03 1991-01-08 Western Research Institute & Ilr Services Inc. Pyrolysis methods with product oil recycling
US4820298A (en) 1987-11-20 1989-04-11 Leveen Eric G Internal vascular prosthesis
US4913141A (en) 1988-10-25 1990-04-03 Cordis Corporation Apparatus and method for placement of a stent within a subject vessel
US4856516A (en) 1989-01-09 1989-08-15 Cordis Corporation Endovascular stent apparatus and method
US5032113A (en) 1989-04-13 1991-07-16 Scimed Life Systems, Inc. Innerless catheter
US5087244A (en) 1989-01-31 1992-02-11 C. R. Bard, Inc. Catheter and method for locally applying medication to the wall of a blood vessel or other body lumen
ATE123658T1 (de) * 1990-06-15 1995-06-15 Cortrak Medical Inc Vorrichtung zur abgabe von medikamenten.
US5318531A (en) * 1991-06-11 1994-06-07 Cordis Corporation Infusion balloon catheter
CA2074304C (fr) 1991-08-02 1996-11-26 Cyril J. Schweich, Jr. Catheter pour l'administration de medicaments
US5368566A (en) * 1992-04-29 1994-11-29 Cardiovascular Dynamics, Inc. Delivery and temporary stent catheter having a reinforced perfusion lumen

Patent Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1995008289A2 (fr) * 1993-09-16 1995-03-30 Scimed Life Systems, Inc. Reparation percutanee d'anomalies cardio-vasculaires et compositions associees

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See also references of WO9618427A1 *

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EP0797463A1 (fr) 1997-10-01
JPH10510730A (ja) 1998-10-20

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