US20050267511A1 - Intracorporeal occlusive device and method - Google Patents

Intracorporeal occlusive device and method Download PDF

Info

Publication number
US20050267511A1
US20050267511A1 US11033463 US3346305A US2005267511A1 US 20050267511 A1 US20050267511 A1 US 20050267511A1 US 11033463 US11033463 US 11033463 US 3346305 A US3346305 A US 3346305A US 2005267511 A1 US2005267511 A1 US 2005267511A1
Authority
US
Grant status
Application
Patent type
Prior art keywords
space filling
filling device
intracorporeal
device
transmutable
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Abandoned
Application number
US11033463
Inventor
Michael Marks
Michael Ross
Original Assignee
Marks Michael P
Michael Ross
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

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/12Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
    • A61B17/12022Occluding by internal devices, e.g. balloons or releasable wires
    • A61B17/12099Occluding by internal devices, e.g. balloons or releasable wires characterised by the location of the occluder
    • A61B17/12109Occluding by internal devices, e.g. balloons or releasable wires characterised by the location of the occluder in a blood vessel
    • A61B17/12113Occluding by internal devices, e.g. balloons or releasable wires characterised by the location of the occluder in a blood vessel within an aneurysm
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/12Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
    • A61B17/12022Occluding by internal devices, e.g. balloons or releasable wires
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/12Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
    • A61B17/12022Occluding by internal devices, e.g. balloons or releasable wires
    • A61B17/12099Occluding by internal devices, e.g. balloons or releasable wires characterised by the location of the occluder
    • A61B17/12109Occluding by internal devices, e.g. balloons or releasable wires characterised by the location of the occluder in a blood vessel
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/12Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
    • A61B17/12022Occluding by internal devices, e.g. balloons or releasable wires
    • A61B17/12131Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device
    • A61B17/12136Balloons
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/12Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
    • A61B17/12022Occluding by internal devices, e.g. balloons or releasable wires
    • A61B17/12131Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device
    • A61B17/1214Coils or wires
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/12Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
    • A61B17/12022Occluding by internal devices, e.g. balloons or releasable wires
    • A61B17/12131Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device
    • A61B17/1214Coils or wires
    • A61B17/12145Coils or wires having a pre-set deployed three-dimensional shape
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/12Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
    • A61B17/12022Occluding by internal devices, e.g. balloons or releasable wires
    • A61B17/12131Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device
    • A61B17/12163Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device having a string of elements connected to each other
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/12Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
    • A61B17/12022Occluding by internal devices, e.g. balloons or releasable wires
    • A61B17/12131Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device
    • A61B17/12181Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device formed by fluidized, gelatinous or cellular remodelable materials, e.g. embolic liquids, foams or extracellular matrices
    • A61B17/12195Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device formed by fluidized, gelatinous or cellular remodelable materials, e.g. embolic liquids, foams or extracellular matrices comprising a curable material
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B2017/00477Coupling
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B2017/00831Material properties
    • A61B2017/00867Material properties shape memory effect
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/12Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
    • A61B17/12022Occluding by internal devices, e.g. balloons or releasable wires
    • A61B2017/1205Introduction devices
    • A61B2017/12054Details concerning the detachment of the occluding device from the introduction device
    • A61B2017/12063Details concerning the detachment of the occluding device from the introduction device electrolytically detachable
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/12Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
    • A61B17/12022Occluding by internal devices, e.g. balloons or releasable wires
    • A61B2017/1205Introduction devices
    • A61B2017/12054Details concerning the detachment of the occluding device from the introduction device
    • A61B2017/12068Details concerning the detachment of the occluding device from the introduction device detachable by heat
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/12Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
    • A61B17/12022Occluding by internal devices, e.g. balloons or releasable wires
    • A61B2017/1205Introduction devices
    • A61B2017/12054Details concerning the detachment of the occluding device from the introduction device
    • A61B2017/12068Details concerning the detachment of the occluding device from the introduction device detachable by heat
    • A61B2017/12072Details concerning the detachment of the occluding device from the introduction device detachable by heat the heat created by laser light
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/12Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
    • A61B17/12022Occluding by internal devices, e.g. balloons or releasable wires
    • A61B2017/1205Introduction devices
    • A61B2017/12054Details concerning the detachment of the occluding device from the introduction device
    • A61B2017/12068Details concerning the detachment of the occluding device from the introduction device detachable by heat
    • A61B2017/12077Joint changing shape upon application of heat, e.g. bi-metal or reversible thermal memory
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/22Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for
    • A61B2017/22051Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for with an inflatable part, e.g. balloon, for positioning, blocking, or immobilisation
    • A61B2017/22065Functions of balloons
    • A61B2017/22068Centering
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00Surgical instruments, devices or methods, e.g. tourniquets
    • A61B17/22Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for
    • A61B2017/22051Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for with an inflatable part, e.g. balloon, for positioning, blocking, or immobilisation
    • A61B2017/22065Functions of balloons
    • A61B2017/22069Immobilising; Stabilising
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES 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
    • A61M25/00Catheters; Hollow probes
    • A61M25/10Balloon catheters
    • A61M2025/1043Balloon catheters with special features or adapted for special applications
    • A61M2025/1052Balloon catheters with special features or adapted for special applications for temporarily occluding a vessel for isolating a sector

Abstract

An intracorporeal space filling device and a delivery system and method for using the device is disclosed. The space filling device is preferably configured for percutaneous delivery from a peripheral conduit of a patient. The space filling device has an elongated tubular or interconnected bead structure which may have a transmutable material disposed within it. The transmutable material can be altered from a non-rigid state to a rigid state by the application of various types of energy or by other suitable means. The space filling device can be positioned by a delivery system and detached from the delivery system after desired positioning is achieved.

Description

  • This application is a continuation of application Ser. No. 10/106,511, filed Mar. 25, 2002 which is a divisional application of application Ser. No. 09/324,987, filed Jun. 2, 1999. The disclosures of these prior applications are incorporated in their entirety herein by this reference.
  • BACKGROUND
  • The present invention is generally directed to occlusion devices and, more specifically, to intracorporeal occlusion devices which can be used to treat a patient's blood vessels, intracorporeal conduits or other portions of a patient's body. A preferred embodiment can be used to treat intracranial aneurysms, arteriovenous fistulas, and other abnormalities within the cerebral vasculature.
  • Cerebral aneurysms and other cerebral vascular abnormalities present a significant medical problem to the population of the United States. It is estimated that the number of ruptured intracranial aneurysms yearly is in the tens of thousands, often with devastating consequences for the patient. For a patient who has been diagnosed with a cerebral aneurysm, there are a few treatment modalities currently available. An invasive surgical treatment can be used where access to the external portion of the aneurysm is achieved by placing the patient under general anesthesia, performing a craniotomy, and brain tissue retraction. Once access has been gained to the external surface of the aneurysm, the neck of the aneurysm can be clipped. Clipping the aneurysm neck prevents the ingress of blood into the aneurysm cavity which can lead to rupture. Because of the invasive nature of the procedure and the vulnerability of the brain tissue surrounding the aneurysm, this procedure carries a high degree of risk with concomitant mortality and morbidity rates. This risk is particularly high when the aneurysm has ruptured prior to the surgical intervention.
  • An alternative to the surgical method currently in use involves percutaneous endovascular intervention. This method generally involves accessing the cerebral aneurysm by means of an intravascular microcatheter which is advanced under flouroscopic imaging over a guidewire or the like within the patient's arteries from a puncture site in the patient's leg or arm. The distal end of the microcatheter is guided over a guidewire within a patient's vasculature and disposed adjacent the neck of the aneurysm. The distal tip of the microcatheter can then be directed into the cavity of the aneurysm and appropriate occlusive devices then delivered from a port in the distal end of the microcatheter. Presently, the most common occlusive device delivered via microcatheter is a vaso-occlusive coil which consists of stainless steel or radiopaque metals such as gold or platinum, tantalum. The vaso-occlusive coils are typically manufactured in a manner similar to the distal coils of a coronary guidewire, having a coil wire material with a small diameter and a coil outer diameter suitable for delivery through a microcatheter. Such vaso-occlusive coils are often given a secondary shape or configuration whereby the coils can be straightened and delivered through the inner lumen of a microcatheter, but form a convoluted or random space filling structure once delivered from the distal end of the microcatheter. The endovascular delivery of vaso-occlusive coils through a microcatheter represents a significant advance in treating cranial aneurysms. However, the coils are hollow bodies, often made of relatively soft metals which are subject to compaction due to the pressure exerted on the deployed coils by the patient's blood flow. Compaction and reforming of the coils leaves them susceptible to dislodging and being displaced within the patient's vasculature, with the potential for causing distal embolization. In addition, compaction of the coils into the dome of the aneurysm or blood clot surrounding the coils can lead to reappearance and regrowth of the aneurysm. Finally, aneurysms with wide necks having a dome to neck dimension ratio of less than 2 to 1 often do not provide a morphology conducive to retention of coils within the aneurysm. Thus currently available coils are generally contraindicated for use in wide neck aneurysms. What has been needed is an intracorporeal space filling device which can be delivered by non-invasive methods, is not subject to compaction or reforming and which is suitable for implantation in wide neck aneurysms.
  • SUMMARY
  • The invention is directed generally to an intracorporeal space filling device and a delivery system for positioning and deploying the space filling device within a patient. The invention is also directed to a method for using the space filling device.
  • One preferred embodiment of the invention is an intracorporeal space filling device which has an elongate tubular shell with a lumen disposed within the shell. The lumen is in fluid communication with a first port in a first end of the shell, and a second port in a second end of the shell. A transmutable material is disposed within the lumen of the shell substantially filling the lumen. The transmutable material has properties which enable transformation from a non-rigid state to a substantially rigid state within a patient's body. The transmutable character of the transmutable material allows for a space filling device that is soft and flexible at the time of deployment into an intracorporeal cavity and rigid and substantially incompressible after being converted to a rigid state. Such a device can conform readily to the varied morphology of intracorporeal cavities and transmute to a substantially rigid mass upon activation or hardening of the transmutable material so as to be resistant to compression and reforming due to vascular or other types of pressures within a patient's body.
  • The elongate shell is generally made of a polymeric wall material and is sealed at either or both of the first and second ends. The transmutable material which fills the lumen of the shell can be selected from a variety of suitable polymers which can be made rigid or hardened by the application of a variety of energy types, such as light emitted from a laser or other source, radiofrequency energy, ultrasonic energy or other suitable means such as controlled changes in the pH of the material surrounding the transmutable material. The space filling device is typically configured for percutaneous delivery through a suitable microcatheter from an incision in a peripheral artery in a patient's arm or leg to a desired intracorporeal cavity, such as a cerebral aneurysm.
  • Optionally, the space filling device may have an elongated longitudinal member secured to and preferably coextensive with the elongate tubular shell of the device. Typically, the elongated longitudinal member is a thin wire member that may or may not be configured to give a secondary shape to the space filling device when in an unconstrained relaxed state. The secondary shape of the longitudinal member can be a convoluted, folded, coiled or twisted configuration or any other suitable space filling configuration when in an unconstrained state which is imparted to the intracorporeal space filling device to which the elongated longitudinal member is secured. When the device is in a linear constrained state or configuration, it may be advanced through an inner lumen of a microcatheter or other similar device for delivery to a desired site within a patient's body. Once the space filling device is removed from the constraint of the microcatheter, it again assumes the space filling secondary shape. The elongated longitudinal member can be made from a variety of suitable materials, including stainless steel and shape memory alloys such as nickel titanium (NiTi). The elongated longitudinal member can be disposed along a longitudinal axis of the space filling device, embedded in the transmutable material, encapsulated within the wall material of the elongate tubular shell, or adjacent an outside surface of the elongate tubular shell or any other suitable location on the device. Preferably the elongate longitudinal member is substantially parallel to the longitudinal axis of the elongate shell or intracorporeal space filling device. The elongated longitudinal member can also be configured to be heated by the passage of various types of energy therethrough. For example, an elongated longitudinal member made of NiTi alloy can be configured to be heated by the passage of electrical current, including radiofrequency, or ultrasonic energy through it. Heating of the elongated longitudinal member can be used to transmute or rigidify the transmutable material within the elongate shell and to act as a mechanism for detachment of the intracorporeal space filling device from the distal end of the delivery system.
  • In a preferred embodiment, the elongate tubular shell is configured to have an outer surface which is self adhering to create attachment points from contact point upon activation of the self adhering outer surface. Contact points along the length of the space filling device inevitably occur when the device is deployed within an intracorporeal cavity or channel and the space filling device assumes a folded or convoluted space filling configuration. The folded or convoluted space filling configuration may be due to the confinement of the void or channel, a secondary shape assumed by the device in a relaxed state, or both. The creation of attachment points results in a more rigid and stable space filling mass that is resistant to compaction and reforming.
  • The intracorporeal space filling device may optionally have a helical coil disposed about an outer surface of the elongate tubular shell. The helical coil may have properties similar to those discussed above with regard to the elongated longitudinal member. For example, the helical coil can be configured to impose a convoluted, folded or space filling secondary shape on the space filling device when in a relaxed unconstrained state. The helical coil may also be configured to heat or otherwise activate transmutation of the transmutable material when various forms of energy are passed through it such as electrical current, ultrasonic energy or the like. The materials of the helical coil may also be similar to those discussed above with regard to the elongated longitudinal member.
  • In an alternative embodiment, the space filling device has a transmutable material disposed about an elongated longitudinal member without an outer shell so that the transmutable material is exposed when the device is deployed within a patient's body. The elongated longitudinal member can have properties similar to those of the elongated longitudinal members discussed above. For example, the elongated longitudinal member can be made of a thin wire with a secondary shape. The secondary shape can be imparted on the space filling device when the device is in an unconstrained state Secondary shapes can include convoluted or folded space filling configurations. Exposure of an outside surface of the transmutable material allows the transmutable material to adhere to itself upon transmutation at attachment points where different portions of the space filling device make contact due to the secondary shape assumed. When the space filling device is deployed in an intracorporeal cavity and assumes a folded, bunched or convoluted configuration due to a secondary shape of the elongated longitudinal member or the natural confinement of the cavity, inevitably, certain portions of the space filling device will make physical contact with other portions of the device. As such, the transmutable material of these portions will make contact at contact points and will cross-link, bond, or self adhere to each other to form attachment points upon transmutation of the transmutable material. The cross-linking or bonding of the device at attachment points results in a rigid mass which is resistive to compression and reforming. The self adhering property of the outside surface of the transmutable material can be as a result of the intrinsic properties of the transmutable material, or as a result of a coating applied to the transmutable material with self adhering properties.
  • In another embodiment, the intracorporeal space filling device has a plurality of beads connected to at least one adjacent bead by a flexible member with connections to adjacent beads being configured to produce a linear array of the beads. Each bead has a transverse dimension and is generally spaced within one transverse dimension of adjacent beads, however, other appropriate spacings are possible. The space filling device of interconnected beads is generally configured for percutaneous delivery through a microcatheter or the like from an incision in a peripheral artery of a patient to a desired cavity within the patient's vasculature such as a cerebral aneurysm. The individual beads typically have a generally spherical shape, but can also be substantially elliptical or elongated. The beads can be made from any suitable material, but are preferably made from a polymer material, and more preferably a transmutable polymer material. In a particular embodiment, the beads may have an outer shell which defines a cavity which optionally contains suitable filler material. Suitable filler materials include biocompatible fluids such as a saline, silicone and the like, and polymers such as a transmutable material similar to the transmutable material discussed above.
  • Embodiments with beads of exposed transmutable material can be cross-linked or bonded to adjacent beads which are in contact at the time of transmutation at a desired site within a patient's body. Adjacent beads in contact while deployed within a desired location within a patient can adhere or bond together and create attachment points upon transmutation of the transmutable material. The attachment points create a more stable and rigid mass than would be achieved by transmutation of the beads without attachment points.
  • The flexible member connecting adjacent beads may consist of interconnected portions of a polymer wall material of the outer shell of each adjacent bead. The flexible member may also be an elongated longitudinal member disposed substantially along a longitudinal axis of the space filling device and being substantially coextensive with at least two adjacent beads of the space filling device. In embodiments of the space filling device having a flexible member consisting of an elongated longitudinal member, the elongated longitudinal member may be a thin wire, preferably of a shape memory alloy. The thin wire longitudinal member can be configured to be heated by a passage of energy through it in order to activate transmutation of transmutable material disposed thereon. The elongated longitudinal member may also be configured to have a secondary shape or space filling configuration in a relaxed state as discussed above with regard to other elongated longitudinal members. The secondary shape or space filling configuration of the elongated longitudinal member would be imparted to the space filling device as a whole when in an unconstrained relaxed state.
  • The intracorporeal space filling devices discussed above are generally deployed at a desired site within a patient's body by disposing the distal end of a microcatheter or the like such that a distal port in the distal end of the microcatheter is directed to a desired cavity or channel within a patient. The space filling device is then distally advanced within the inner lumen of the microcatheter, preferably by means of a delivery system which has an elongate shaft with a detachment mechanism disposed on the distal end of the system. The detachment mechanism is detachably secured to a first end of the space filling device which provides a detachable connection and allows for remote advancement and retraction of the space filling device within the patient prior to detachment. The space filling device is then distally advanced out of a port in the distal end of the microcatheter and into the cavity or channel of the patient. When the space filling device is appropriately positioned, the transmutable material within the device is activated so as to be hardened or rigidified, and the device detached from the delivery system. Preferably, the space filling device is detached by a detachment mechanism utilizing degradation of a polymer link between the delivery system and the first end of the space filling device. Degradation of the polymer link may be accomplished by a chain cleavage reaction which can be initiated by heating of the polymer link. Alternative detachment mechanisms include mechanical detachment, electrolytic detachment, detachment by shape memory alloy or shape memory polymer activation via application of RF energy, laser energy or ultrasonic energy, heating of a hot melt adhesive joint, ultrasonic link degradation, hydrokinetic pressure activation of a mechanical retention device, and the like.
  • During deployment of a space filling device, a blocking balloon may be deployed adjacent the opening of an intracorporeal void and distal end of a microcatheter disposed within the void prior to distally advancing the space filling device from the distal end of the microcatheter into the cavity. The blocking balloon prevents egress of the space filling device from within the cavity during deployment of the device.
  • These and other advantages of the invention will become more apparent from the following detailed description of the invention when taken in conjunction with the accompanying exemplary drawings.
  • BRIEF DESCRIPTION
  • FIG. 1 is a longitudinal sectional view of an intracorporeal space filling device having features of the invention.
  • FIG. 2 is a transverse cross sectional view of the intracorporeal space filling device of FIG. 1 taken at lines 2-2 of FIG. 1.
  • FIG. 3 is a longitudinal sectional view of an intracorporeal space filling device having features of the invention.
  • FIG. 4 is a transverse cross sectional view of the intracorporeal space filling device of FIG. 3 taken at lines 4-4 of FIG. 3.
  • FIG. 5 is a longitudinal sectional view of an intracorporeal space filling device having features of the invention.
  • FIG. 6 is a transverse cross sectional view of the intracorporeal space filling device of FIG. 5 taken at lines 6-6 of FIG. 5.
  • FIG. 7 is a longitudinal sectional view in of an intracorporeal space filling device similar to the device of FIG. 1, but including an outer coil member.
  • FIG. 8 is a transverse cross sectional view of the device of FIG. 7 taken along lines 8-8 in FIG. 7.
  • FIG. 9 is a longitudinal sectional view of an intracorporeal space filling device having features of the invention.
  • FIG. 10 is a transverse cross sectional view of the intracorporeal space filling device of FIG. 9 taken at lines 10-10 of FIG. 9.
  • FIG. 11 is a transverse cross sectional view of the intracorporeal space filling device of FIG. 9 taken at lines 11-11 of FIG. 9.
  • FIG. 12 is a longitudinal sectional view of an intracorporeal space filling device having features of the invention.
  • FIG. 13 is a transverse cross sectional view of the intracorporeal space filling device of FIG. 12 taken at lines 13-13 of FIG. 12.
  • FIG. 14 is a longitudinal sectional view of an intracorporeal space filling device having features of the invention.
  • FIG. 15 is a transverse cross sectional view of the intracorporeal space filling device of FIG. 14 taken at lines 15-15 of FIG. 14.
  • FIG. 16 is a schematic view in partial longitudinal section of a microcatheter over a guidewire disposed within a patient's blood vessel.
  • FIG. 17 is a schematic view in partial section of the distal end of a microcatheter disposed within the neck of an aneurysm.
  • FIG. 18 is a schematic view in partial section of the distal end of a microcatheter disposed within an aneurysmal cavity with an intracorporeal space filling device deployed within the aneurysm.
  • FIG. 19 is a schematic view in partial section of a blocking balloon deployed adjacent an aneurysm with the distal end of a microcatheter disposed within the aneurysm and an intracorporeal space filling device disposed within the aneurysm.
  • FIG. 20 is an elevational view in partial section of a first end of an intracorporeal space filling device detachably secured to a distal end of a delivery system having features of the invention.
  • FIG. 21 is an elevational view in partial section of a first end of an intracorporeal space filling device detachably secured to a distal end of a delivery system having features of the invention.
  • FIG. 22 is an elevational view in partial section of a first end of an intracorporeal space filling device detachably secured to a distal end of a delivery system having features of the invention.
  • FIG. 23 is an elevational view in partial section of a first end of an intracorporeal space filling device detachably secured to a distal end of a delivery system having features of the invention.
  • FIGS. 24-26 depict an alternative embodiment of a capture element for detachment of the space filling device.
  • DETAILED DESCRIPTION
  • FIG. 1 illustrates an intracorporeal space filling device 10 having features of the invention. The intracorporeal space filling device 10 has an optional elongate tubular shell 11 with a first end 12 and a second end 13, the elongate shell being formed of a wall material 14. There is a lumen 15 disposed within the elongate tubular shell 11 which has transmutable material 16 disposed therein.
  • The elongate tubular shell 11 can be made from a variety of materials including metals and polymers. Suitable metals for the elongate tubular shell include stainless steel, NiTi, gold, platinum, tantalum, palladium, alloys thereof and the like. If a metal or other rigid material is used, methods such as forming slots or grooves in the wall material of such an elongate tubular shell may be used to achieve a desired longitudinal flexibility of the elongate tubular shell 11. Suitable polymers for the elongate tubular shell 11 can include polyurethane, polyethylene, nylon, polyimide, polyamide, polytetraflouroethylene, polyester, polypropylene and the like. The elongate tubular shell 11 may be sealed and impermeable to the transmutable material 16, so as to prevent the egress of the transmutable material from within the shell to the surrounding environment.
  • In one preferred embodiment, the elongate tubular shell 11 has at least one aperture which exposes the transmutable material 16 and allows the transmutable material to make contact with adjacent portions of the space filling device or other space filling devices so as to permit self adhering or bonding upon transmutation of the transmutable material. The apertures in the elongate tubular shell 11 can be in the form of transverse or longitudinal slots or grooves, circular or otherwise configured holes, or the like. The apertures may be relatively far apart relative to the size of the apertures, or they may be relatively close together and numerous so as to form a mesh pattern or other suitable pattern of fenestration which facilitates exposure of the transmutable material 16 but maintains the overall elongated structure of the space filling device 10. Similar apertures may be appropriate for any of the various embodiments of space filling devices discussed herein having outer shell structures.
  • The dimensions of the space filling device 10 and elongate tubular shell 11 are generally appropriate for percutaneous delivery via a microcatheter to a desired site within a patient's vasculature, however, other suitable dimensions and configurations are contemplated. The length of the space filling device 10, and all other embodiments of space filling devices discussed herein generally, can be from about 0.5 to about 50 cm, preferably about 2 to about 30 cm. It should be noted that the morphology of the sites being filled or otherwise treated by the present invention vary greatly. Embodiments of the invention for use treating cerebral aneurysms may be made available in a variety of sizes and lengths so that most of the anticipated morphologies can be accommodated. For example, a space filling device 10, and other space filling devices discussed herein generally, configured for treatment of cerebral aneurysms, or the like, may be made available in lengths of 2, 5, 10, 15, 20, 25, 30, 35 and 40 cm. In this way, a wide range of aneurysm volumes can be appropriately treated.
  • A transverse dimension of the space filling device 10, and of all other embodiments of space filling device discussed herein generally, can be from about 0.005 to about 0.25 inches, preferably about 0.01 to about 0.038 inches, and more preferably about 0.014 to about 0.018 inches. In other preferred embodiments of the invention, the transverse dimension of the space filling device can be from about 0.004 to about 0.02 inches, preferably about 0.008 to about 0.012 inches. The thickness of the wall material 14 of the elongate tubular shell 11 can be from about 0.0001 to about 0.01 inches, preferably about 0.0005 to about 0.002 inches, and more preferably about 0.001 to about 0.0015 inches.
  • The transmutable material 16 disposed within the elongate tubular shell 11 is preferably a material that can be transmuted by polymerization, crystallization or other suitable process from a non-rigid liquid, gel or granular state to a rigid state. Some of the materials suitable for this application are discussed generally in U.S. Pat. No. 5,334,201, K. Cowan, and U.S. Pat. No. 5,443,495, P. Buscemi, et al., which are hereby incorporated by reference in their entirety. Transmutation of the transmutable material can be achieved or activated by the application of a suitable type of energy to the transmutable material. Suitable types of energy include electromagnetic energy in the form of light, DC current, AC current, RF current or the like in addition to ultrasonic energy. Energy may also be applied directly or indirectly in the form of heat to cause transmutation. Transmutation may also be activated by altering the chemistry of the environment surrounding the transmutable material such as by changing the pH or by injection of a catalyst into the transmutable materials, either directly or indirectly by injection or introduction into the surrounding tissue or bodily fluid such a blood. With regard to the embodiment of FIG. 1, laser or RF energy is preferably applied to the outer surface of the elongate tubular shell and transmutable material to cause transmutation. The outer dimensions of the transmutable material 16 are generally similar to the cavity dimensions of the elongate tubular shell 11. As an alternative to the transmutable material 16, any suitable biocompatible filler material may be used such as saline, silicone or the like. Such alternative filler materials may be used within any of the suitable embodiments of space filling devices described herein, either as an alternative to a transmutable material, or in addition to a transmutable material. Embodiments of the invention suitable for alternative filler materials are generally those embodiments having a shell structure configured to confine the alternative filler materials.
  • In embodiments of the space filling device 10 where the transmutable material 16 is exposed, that is, where the optional elongate tubular shell 11 is not present, or portions of the elongate tubular shell 11 are not present at aperture sites, it is preferable that the transmutable material 16 be self adhering in a fluid field, such as blood or saline. In this way, when the device 10 is deployed within an intracorporeal cavity or channel and folds back on itself as a result of the confinement of the cavity or channel, any contact points between transmutable material where the device is folded on itself and making mechanical contact will become attachment points upon transmutation of the transmutable material by bonding or adhering to itself at the contact points. The attachment points result in a more stable space filling mass that is resistant to compaction and reforming.
  • Suitable substances generally for the transmutable material 16 include methacrylate compounds, linear polyester, silicone, cyanoacrylates, polyisocyanate, u.v. curable acrylates, moisture cure silicones, dimethyl sulfoxide, thioisocyanate aldehyde, isocyanate, divinyl compounds, epoxide acrylates, succinimidyl azido salicylate, succinimidyl azidobenzoate, succinimidyl dithio acetate, azidoiodobenzene, flouronitrophenylazide, salicylate azides, benzophenonemaleimide, and the like.
  • FIG. 2 is a transverse cross sectional view of the intracorporeal space filling device 10 of FIG. 1. The transmutable material 16 is disposed within the optional elongate tubular shell 11 of the device. The cross section of FIG. 2 is shown as substantially round, however, other suitable cross sectional configurations can be used such as elliptical, triangular or square.
  • FIGS. 3 and 4 illustrate an intracorporeal space filling device 20 similar to the embodiment of FIG. 1, with the addition of an elongated longitudinal member 21 disposed along a longitudinal axis 22 of the optional elongate tubular shell 23. The materials, dimensions, and features of the elongated tubular shell 23 of FIGS. 3 and 4 can be similar to those of the elongated tubular shell 11 of FIGS. 1 and 2. The materials and dimensions of the transmutable material 24 can be similar to those of the transmutable material 16 discussed above. Typically, the elongated longitudinal member 21 is a thin wire member that is configured to give a secondary shape to the space filling device when in an unconstrained relaxed state. The longitudinal member 21 can have a secondary shape of a convoluted, folded, coiled or twisted configuration or any other suitable space filling configuration when in an unconstrained state. This configuration is imparted to the intracorporeal space filling device 20 to which the elongated longitudinal member 21 is secured. When the device 20 is in a linear constrained state or configuration, it may be advanced through an inner lumen of a microcatheter or other similar device for delivery to a desired site within a patient's body. Once the space filling device 20 is removed from the constraint of the microcatheter, it again assumes the space filling configuration. The space filling device 20, and all other space filling devices described herein generally which are configured to have a secondary space filling shape, may have a variety of nominal transverse dimensions or diameters when in a secondary shape. In order to conform to a wide variety of intracorporeal morphologies, the space filling device may have a secondary shape with a transverse dimension of between about 1 to about 20 mm. A typical space filling device maybe made with a secondary shape having a transverse dimension of between 1 and 20 mm, in 1 mm increments.
  • The elongated longitudinal member 21 can be made from a variety of suitable materials, including stainless steel and shape memory alloys such as nickel titanium (NiTi). The length of the elongated longitudinal member 21 can be from about 0.5 to about 50 cm, preferably about 1 to about 20 cm, and more preferably about 5 to about 15 cm. It is preferable that the elongated longitudinal member 21 be coextensive with the length of the elongated tubular shell 23 and with the space filling device generally. Thus, the elongated longitudinal member may have any of the lengths discussed herein with regard to space filling devices. The transverse dimension of the elongated longitudinal member 21 can be from about 0.0005 to about 0.01 inches, preferably about 0.001 to about 0.003 inches, and more preferably about 0.0015 to about 0.002 inches. The cross section of the elongated longitudinal member is generally round, however, other configurations are contemplated. Alternative cross sectional shapes for the elongated longitudinal member include elliptical, rectangular, as would be found if a flat ribbon wire used, triangular, square and the like. The various cross sections can be chosen to give a desired preferred bend axis or axes along the length of the member. Preferably the elongate longitudinal member is substantially parallel to the longitudinal axis 22 of the elongate shell or intracorporeal space filling device. The elongated longitudinal member 21 can also be configured to be heated by the passage of various types of energy therethrough. For example, an elongated longitudinal member 21 made of NiTi alloy can be configured to be heated by the passage of electrical current through it. Heating of the elongated longitudinal member 21 can be used to transmute or rigidify the transmutable material within the elongate tubular shell 23 and to act as a mechanism for detachment of the intracorporeal space filling device 20 from a distal end of a delivery system.
  • FIGS. 5 and 6 show an embodiment of an intracorporeal space filling device 30 similar to the embodiment of FIGS. 3 and 4 but having an elongated longitudinal member 31 encapsulated within a wall material 32 of the elongated tubular shell 33. The materials, dimensions and features of the elongated tubular shell 33 and elongated longitudinal member 31 of FIGS. 5 and 6 are similar to those of the elongated tubular shell 23 and elongated longitudinal member 21 of FIGS. 3 and 4. The elongated longitudinal member 31 may also be secured to an outside surface 34 or inside surface 36 of the elongate tubular shell 33 by an adhesive or other suitable means. A transmutable material 35 disposed within the elongate tubular shell 33 can have properties and dimensions similar to or the same as those of transmutable materials 16 and 24 of FIGS. 1-4 above.
  • FIGS. 7 and 8 illustrate an intracorporeal space filling device 40 similar to that of FIGS. 1 and 2, but with a helical coil 41 disposed about an outside surface 42 of the elongated tubular shell 43. The helical coil 41 of FIGS. 7 and 8 may have some properties similar to those discussed above with regard to the elongated longitudinal members 21 and 31 of FIGS. 3-6. The helical coil 41 can be configured to impose a convoluted, folded or space filling configuration on the space filling device 40 when in a relaxed unconstrained state. The helical coil 41 may also be configured to heat when various forms of energy are passed through it. The materials of the helical coil 41 can be any suitable metal, composite or polymer including shape memory alloys such as NiTi or high strength alloys such as stainless steel. The type and dimensions of the material from which the helical coil 41 is made can be similar to the elongated longitudinal member 31 discussed above. A transmutable material 44 is disposed within the elongated tubular shell 43 and can have properties similar or identical to the properties of transmutable materials 16, 24 and 35 of FIGS. 1-6 above.
  • FIGS. 9-11 depict an alternative embodiment of an intracorporeal space filling device 50 having a plurality of beads 51 secured to each other in a linear configuration. The intracorporeal space filling device 50 has a plurality of beads 51 connected to at least one adjacent bead by a flexible member 52 with connections to adjacent beads preferably being configured to produce a linear array of the beads. Each bead 51 has a transverse dimension and is generally spaced within one transverse dimension of adjacent beads, however, other appropriate spacings are possible. The space filling device 50 is generally configured for percutaneous delivery through a microcatheter or the like from an incision in a peripheral artery of a patient to a desired cavity within the patient's vasculature such as a cerebral aneurysm. The individual beads 51 typically have a generally spherical shape, but can also be substantially elliptical, with the elliptical shape optionally being elongated longitudinally to a length of multiple transverse dimensions. The beads 51 can be made from a rigid homogeneous polymer material, but are preferably made from an outer shell 53 which defines a cavity 54 such as is shown in FIGS. 9-11. The outer shell 53 can be made from a variety of materials including metals and polymers. Suitable metals for the shell 53 include stainless steel, NiTi, gold, platinum, tantalum, palladium, alloys thereof and the like. If a metal or other rigid material is used, methods such as forming slots or grooves in the wall material of the shell may be used to achieve a desired longitudinal flexibility. Suitable polymers for the shell 53 can include polyurethane, polyethylene, nylon, polyimide, polyamide, polytetraflouroethylene, polyester, polypropylene and the like. The outer shell 53 may have apertures similar to those of space filling device 10 described above for exposing portions of transmutable material contained therein which facilitates self adherence and the creation of attachment points upon transmutation of the transmutable material.
  • The cavity 54 optionally contains a transmutable material 55 similar to the transmutable materials 16, 24, 35 and 44 discussed above. The transmutable material 55 is preferably a material that can be transmuted by polymerization, crystallization or other suitable process from a non-rigid liquid, gel or granular state to a rigid state. Transmutation of the transmutable material 55 can be achieved or precipitated by the application of a suitable type of energy to the transmutable material such as electromagnetic energy in the form of light, DC current, AC current, RF or ultrasonic energy. Energy may also be applied directly or indirectly in the form of heat to cause transmutation. Other methods of causing or precipitating transmutation can include altering the pH of the surrounding environment of the transmutable material, or injecting a catalyst into the transmutable material directly, or indirectly by injecting a catalyst into the environment of the transmutable material.
  • The dimensions of the space filling device 50 overall are similar to those of the previously discussed embodiments. The thickness of the wall material 56 of the outer shell 53 can be from about 0.0001 to about 0.01 inches, preferably about 0.0005 to about 0.002 inches, and more preferably about 0.001 to about 0.0015 inches. The wall material 56 of the outer shell 53 of the beads 51 and the transmutable material 55 disposed within the outer shell can be similar to the materials of the elongate tubular shell 11 and transmutable material 16 of the embodiment of FIG. 1.
  • The flexible member 52 connecting adjacent beads may consist of interconnected portions of a polymer wall material 56 of the outer shell 53 of each adjacent bead as shown in FIGS. 9-11. As shown in FIGS. 12-13, an intracorporeal space filling device 60 may have flexible members 61 that consist of portions of an elongated longitudinal member 62 disposed substantially along a longitudinal axis 63 of the space filling device 60 and being substantially coextensive with at least two adjacent beads 64 of the space filling device. The beads 64 of the space filling device 60 are made of a polymer material 65 which is a transmutable material. The exposed outer surface of the transmutable material of the beads 64 is self adhering in a fluid field, such as blood or saline. When the space filling device 60 is deployed within a body cavity and folds back on itself as a result of the confinement or secondary shape, any contact points where the device is folded on itself making mechanical contact will become attachment points upon transmutation of the transmutable material of the beads 64. The attachment points result in a more stable space filling mass which is resistant to compaction and reforming.
  • The elongated longitudinal member 62 may be a thin wire, preferably of a shape memory alloy that can be configured to be heated by a passage of energy through it. The elongated longitudinal member 62 shown in FIGS. 12-13 can have similar dimensions and properties to the elongated longitudinal members 21 and 31 shown in FIGS. 3-6. These properties can include a secondary shape, shape memory properties, and heating upon a passage of energy through the elongate longitudinal member 62. In addition, the elongated longitudinal member 62 can have a variety of cross section configuration including round, square, rectangular and the like.
  • FIGS. 14 and 15 depict an intracorporeal space filling device 66 which has beads 67 attached in a substantially linear array by an elongate longitudinal member 68. The beads 67 have an outer shell 69 which is optionally filled with a transmutable material 69A. The dimensions and materials of beads 67 can be similar to those of beads 51 discussed above with regard to FIGS. 9-11. The materials and dimensions of longitudinal member 68 can be similar to those of elongated longitudinal member 62 discussed above with respect to FIGS. 12 and 13.
  • FIGS. 16-19 schematically depict a procedure whereby an intracorporeal space filling device 70 is deployed within an intravascular cerebral aneurysm 71 of a patient by percutaneous means through a lumen 72 of a microcatheter 73. The distal end 74 of microcatheter 73 is advanced over a guidewire 75 through a patient's vasculature and artery 76 to an aneurysm 71. The space filling device 70 is then distally advanced within an inner lumen 72 of the microcatheter 73, preferably by means of a delivery system 77. Delivery system 77 has an elongate shaft 80 with a detachment mechanism 81 disposed on the distal end 82 of the system. The detachment mechanism 81 is detachably secured to a first end 83 of the space filling device 70 which allows proximal manipulation of the delivery system 77 to control axial advancement and retraction of the space filling device within the microcatheter 73 and the patient. The space filling device 70 is then distally advanced out of a port 84 in the distal end 74 of the microcatheter 73 and into the aneurysm 71.
  • When the space filling device 70 is appropriately positioned, transmutable material of device 70 is transmuted to a rigid state, and the space filling device 70 detached from the delivery system 77. Transmutation of the transmutable material may take place prior to, during or after detachment of the space filling device from the detachment mechanism. The space filling device 70 is detached by degradation of a polymer link 85 between the delivery system 70 and the first end 83 of the space filling device, preferably by a chain cleavage reaction which can be initiated by heating of the polymer link 85. Although the illustrated method of detachment of the space filling device 70 is chain cleavage degradation of a polymer link 85, any suitable detachment method may be used. Examples of suitable detachment methods include mechanical detachment, electrolytic detachment, shape memory metal or polymer activation via a temperature change by application of RF energy, laser energy, ultrasonic energy, heating of a hot melt adhesive joint, ultrasonic joint degradation, hydrokinetic activation of a mechanical retaining device, and the like. Various detachment mechanisms known in the art are discussed in U.S. Pat. No. 5,722,989, J. Fitch et al: U.S. Pat. No. 5,108,407, G. Geremia et al., U.S. Pat. No. 5,217,484, M. Marks, and U.S. Pat. No. 5,423,829, P. Pham, which are hereby incorporated by reference.
  • Upon proper positioning of the space filling device 70 within the aneurysm 71, the device will assume a space filling folded or convoluted configuration due to the confinement of the aneurysm cavity, a secondary shape imparted to the device by an elongated longitudinal member having a secondary shape, or both of these. As a result of the folded or convoluted configuration of the space filling device, contact points 78 as shown in the enlarged view of FIG. 18A will result. Upon transmutations of the transmutable material of the device 70, contact points 78 cross-link, bond, self adhere or the like to become attachment points which result in a more stable and rigid transmuted space filling device than would result without such attachment points. Such a configuration resists compaction and repositioning after deployment, and facilitates use in aneurysms or other bodily cavities having a dome to neck ratio of less than 2 to 1. It is believed that upon proper deployment of the space filling device of the present invention, flow of blood throughout the aneurysm will be sufficiently reduced for a sufficient time to allow clot formation within the aneurysm cavity. Eventually, the clot will organize and endothelial growth over the clot in the neck area of the filled aneurysm will ensue, completing the healing process. The resistance to compaction and reforming by the space filling device of the present invention is believed to facilitate the reduction of blood flow throughout the aneurysm for a sufficient time for this healing process to occur.
  • As shown in FIG. 19, a blocking balloon 86 may be deployed adjacent the neck of aneurysm 87 and distal end 74 of the microcatheter 73 prior to distally advancing the space filling device from the distal end of the microcatheter into the aneurysm. The blocking balloon 86 facilitates maintaining the space filling device 70 within the aneurysm 71 prior to transmutation of the transmutable material within the space filling device. In this way, aneurysms having a greater neck to dome ratio can be effectively treated.
  • FIG. 20 shows a distal end 90 of a delivery system 91 detachably secured to a first end 92 of a space filling device 93 having features of the invention. The distal end 90 of the delivery system has an elongate tubular shaft 94 with an inner lumen 95 disposed therein. A detachment signal conduit 96 is disposed within the inner lumen 95 of the shaft and is connected to a degradable polymer link 97 at a distal extremity 98 of the conduit. A first end 101 of an elongate longitudinal member 102 is detachably secured to the degradable polymer link 97 to form a detachment mechanism 103. The detachment mechanism 103 can be activated by means of a signal transmitted through the detachment signal conduit 96 which degrades the polymer link and releases the space filling device 93 from the delivery system 91. The polymer link 97 is preferably degraded by a chain cleavage or scission reaction. Materials and methods suitable for such a mechanism are discussed generally in U.S. Pat. No. 5,443,495 which has been incorporated herein. The detachment signal transmitted through the detachment signal conduit 96 is preferably a radiofrequency signal that initiates a chain cleavage reaction in the degradable polymer link 97, however, other signals or energy delivery may be used such as alternating or direct electric current, ultrasonic energy, laser energy or any other form of electromagnetic radiation or the like. The detachment signal conduit 96 may be a single, double or multiple pole wire, coaxial cable, fiber optic, elongate ultrasonic energy transmitter, such as a solid rod of metal, glass or composite or the like. If a single pole wire is used, a current flow path may be established by the application of a conductive pad to a suitable portion of the patient's body, preferably with a highly conductive gel between the conductive pad and the patient's skin. Alternatively, a conductive needle, such as a stainless steel 18 gauge needle, may be inserted into a suitable site of the patient to act as a ground. These grounding techniques may be used for any port of the invention requiring an electric current flow path, including the heating of elongated longitudinal or helical members for transmutation of transmutable materials.
  • FIG. 21 shows a distal end 107 of a delivery system 108 detachably secured to a first end 109 of a space filling device 111 having features of the invention. The distal end 107 of the delivery system 108 has an elongate tubular shaft 112 with an inner lumen 113 disposed therein. A detachment signal conduit 114 is disposed within the inner lumen 113 of the shaft 112 and is connected to a degradable polymer link 115 at a distal extremity 116 of the conduit. The first end 109 of the space filling device 111 is detachably secured to the degradable polymer link 115 to form a detachment mechanism 118. The detachment mechanism 118 can be activated by means of a signal transmitted through the detachment signal conduit 114 which degrades the polymer link 115 and releases the space filling device 111 from the delivery system 108. The detachment signal transmitted through the detachment signal conduit 114 is preferably a low voltage direct current electric signal that heats a resistive element 119 and initiates a chain cleavage reaction in the degradable polymer link 115. However, other signals or energy delivery may be used such as alternating or direct electric current, ultrasonic energy, laser energy or any other form of electromagnetic radiation or the like. The detachment signal conduit 114 may be a single, double or multiple pole wire, coaxial cable, fiber optic, elongate ultrasonic energy transmitter, such as a solid rod of metal, glass or composite or the like.
  • FIG. 22 shows a distal end 121 of a delivery system 122 detachably secured to a first end 123 of a space filling device 124 having features of the invention. The distal end 121 of the delivery system has an elongate tubular shaft 125 with an inner lumen 126 disposed therein. A detachment signal conduit 127 is disposed within the inner lumen 126 of the shaft 125 and is connected to a mechanical capture device 128 at a distal extremity 129 of the conduit. A first extremity 131 of an elongate longitudinal member 132 has an enlarged portion 133 which is mechanically captured by a plurality of capture elements 135 of the mechanical capture device 128. The capture elements 135 can be activated by means of a signal transmitted through the detachment signal conduit 127 which causes the capture elements 135 to expand in an outward radial direction which releases the enlarged portion 133 of the elongated longitudinal member 132 and releases the space filling device 124 from the delivery system 122. The detachment signal transmitted through the detachment signal conduit is preferably a low voltage electrical signal that heats the capture elements 135 which are made of a shape memory alloy such as NiTi and which are configured to have a remembered shape in an open expanded position which results upon heating of the elements. A similar result can be achieved in an alternative embodiment of a mechanical capture device which has capture elements which are radially constrained by an elongated tubular detachment signal conduit. Upon longitudinal retraction of the tubular conduit, the constraint of the capture elements is removed and an enlarged portion released. Alternative detachment signals include alternating or direct electric current, ultrasonic energy, laser energy or any other form of electromagnetic radiation or the like. The detachment signal conduit may be a single, double or multiple pole electrically conducting wire, coaxial cable, fiber optic, elongate tubular member with an inner lumen for conduction of hydrokinetic energy and activation of a hydrokinetic detachment mechanism, elongate ultrasonic energy transmitter, such as a solid rod of metal, glass or composite or the like. The detachment signal may also be in the form of mechanical actuation by longitudinal or rotational translation of a mechanical detachment signal conduit such as an elongate rod, shaft, or tubular member.
  • FIG. 23 shows a distal end 138 of a delivery system 139 detachably secured to a first end 141 of a space filling device 142 having features of the invention. The distal end 138 of the delivery system has an elongate tubular shaft 143 with an inner lumen 144 disposed therein. A detachment signal conduit 145 is disposed within the inner lumen 144 of the shaft 143 and is connected to a mechanical capture device 146 at a distal extremity 147 of the conduit. A first extremity 148 of an elongate longitudinal member 149 has an enlarged portion 151 which is mechanically captured by a helical capture element 152 of the mechanical capture device 146. The helical capture element 152 can be activated by means of a signal transmitted through the detachment signal conduit 145 which causes the capture element 152 to expand in an outward radial direction which releases the enlarged portion 151 of the elongated longitudinal member 149 and releases the space filling device 142 from the delivery system 139. The detachment signal transmitted through the detachment signal conduit 145 is preferably a low voltage electrical signal that heats the capture element 152 which is made of a shape memory alloy such as NiTi and which is configured to have a remembered shape in an open expanded position which results upon heating of the element. Alternative detachment signals include alternating or direct electric current, ultrasonic energy, laser energy or any other form of electromagnetic radiation or the like. The detachment signal conduit 145 may be a single, double or multiple pole wire, coaxial cable, fiber optic, elongate ultrasonic energy transmitter, such as a solid rod of metal, glass or composite or the like.
  • An alternative capture element for the mechanical capture device could include a tubular member, preferably in the form of a braided capture element 160 as shown in FIGS. 24-26. The braided capture element 160 as shown is constructed of braided elongated filaments 161 of a shape memory alloy, such as NiTi alloy. The capture element 160 could also be a tubular member of shape memory polymer with similar properties. The elongated filaments 161 are arranged in a braided tubular structure with a first inner diameter 162 which is smaller than a nominal diameter or transverse dimension of an enlarged potion 163, and which mechanically surrounds and captures the enlarged portion. The braided tubular structure of the capture element also has a second remembered inner diameter 171 or transverse dimension which is greater than the transverse dimension of the enlarged portion 163. In this way, the space filling device 164 can be introduced into a desired area of a patient while secured to a distal end 165 of a delivery system 166 by the mechanical pressure of the first inner diameter 162 of the braided capture element 160 on the enlarged portion 163 of the first end 166 of the elongated longitudinal member 167 of the space filling device 168. Upon placement of the space filling device 168 within the desired area within a patient, the shape memory elongated filaments 161 can be activated so as to remember the larger second inner diameter 171 releasing the enlarged portion and the space filling device into the desired area of the patient as indicated by arrow 172. Activation of the braided capture element 160 could be carried out by the application of energy by the various methods described above. Such an embodiment of the capture element, as well as any other embodiment of the capture element discussed above, could be used to detach any of the various embodiments of the space filling device discussed herein.
  • While particular forms of the invention have been illustrated and described, it will be apparent that various modifications can be made without departing from the spirit and scope of the invention. Accordingly, it is not intended that the invention be limited, except as by the appended claims.

Claims (1)

  1. 1. A method of occluding an intracorporeal void, comprising:
    (a) positioning the distal end of a microcatheter such that a distal port in the distal end is directed to the cavity of the intracorporeal void;
    (b) distally advancing an intracorporeal space filling device comprising:
    an elongate tubular shell which has a first port disposed at a first end and a second port disposed at a second end and an inner lumen disposed within the shell in fluid communication with the first port and second port; and
    a transmutable material disposed within the inner lumen of the shell that is transmutable from a non-rigid state to a substantially rigid state within the patient's body,
    (c) deploying the space filling device into the void
    (d) transmuting the transmutable material from a non-rigid state to a substantially rigid state;
    (e) detaching the space filling device from the delivery system by activation of a detachment mechanism after the space filling device has been positioned with the intracorporeal void.
US11033463 1999-06-02 2005-01-11 Intracorporeal occlusive device and method Abandoned US20050267511A1 (en)

Priority Applications (3)

Application Number Priority Date Filing Date Title
US32498799 true 1999-06-02 1999-06-02
US10106511 US20020099408A1 (en) 1999-06-02 2002-03-25 Method and apparatus for detaching an intracorporeal occlusive device
US11033463 US20050267511A1 (en) 1999-06-02 2005-01-11 Intracorporeal occlusive device and method

Applications Claiming Priority (6)

Application Number Priority Date Filing Date Title
US11033463 US20050267511A1 (en) 1999-06-02 2005-01-11 Intracorporeal occlusive device and method
US11169322 US20060079929A1 (en) 1999-06-02 2005-06-28 Intracorporeal occlusive device and method
US11418551 US8932317B2 (en) 1999-06-02 2006-05-03 Intracorporeal occlusive device and method
US11418488 US20060265001A1 (en) 1999-06-02 2006-05-03 Intracorporeal occlusive device and method
US12275126 US9526505B2 (en) 1999-06-02 2008-11-20 Intracorporeal occlusive device and method
US14574230 US9788840B2 (en) 1999-06-02 2014-12-17 Intracorporeal occlusive device and method

Related Parent Applications (1)

Application Number Title Priority Date Filing Date
US10106511 Continuation US20020099408A1 (en) 1999-06-02 2002-03-25 Method and apparatus for detaching an intracorporeal occlusive device

Related Child Applications (1)

Application Number Title Priority Date Filing Date
US11169322 Continuation US20060079929A1 (en) 1999-06-02 2005-06-28 Intracorporeal occlusive device and method

Publications (1)

Publication Number Publication Date
US20050267511A1 true true US20050267511A1 (en) 2005-12-01

Family

ID=23265963

Family Applications (7)

Application Number Title Priority Date Filing Date
US10106511 Abandoned US20020099408A1 (en) 1999-06-02 2002-03-25 Method and apparatus for detaching an intracorporeal occlusive device
US11033463 Abandoned US20050267511A1 (en) 1999-06-02 2005-01-11 Intracorporeal occlusive device and method
US11169322 Abandoned US20060079929A1 (en) 1999-06-02 2005-06-28 Intracorporeal occlusive device and method
US11418551 Active 2021-05-15 US8932317B2 (en) 1999-06-02 2006-05-03 Intracorporeal occlusive device and method
US11418488 Abandoned US20060265001A1 (en) 1999-06-02 2006-05-03 Intracorporeal occlusive device and method
US12275126 Active 2022-06-11 US9526505B2 (en) 1999-06-02 2008-11-20 Intracorporeal occlusive device and method
US14574230 Active 2020-02-05 US9788840B2 (en) 1999-06-02 2014-12-17 Intracorporeal occlusive device and method

Family Applications Before (1)

Application Number Title Priority Date Filing Date
US10106511 Abandoned US20020099408A1 (en) 1999-06-02 2002-03-25 Method and apparatus for detaching an intracorporeal occlusive device

Family Applications After (5)

Application Number Title Priority Date Filing Date
US11169322 Abandoned US20060079929A1 (en) 1999-06-02 2005-06-28 Intracorporeal occlusive device and method
US11418551 Active 2021-05-15 US8932317B2 (en) 1999-06-02 2006-05-03 Intracorporeal occlusive device and method
US11418488 Abandoned US20060265001A1 (en) 1999-06-02 2006-05-03 Intracorporeal occlusive device and method
US12275126 Active 2022-06-11 US9526505B2 (en) 1999-06-02 2008-11-20 Intracorporeal occlusive device and method
US14574230 Active 2020-02-05 US9788840B2 (en) 1999-06-02 2014-12-17 Intracorporeal occlusive device and method

Country Status (5)

Country Link
US (7) US20020099408A1 (en)
EP (4) EP1867300A3 (en)
DE (2) DE60037025D1 (en)
ES (2) ES2555961T3 (en)
WO (1) WO2000072781A3 (en)

Cited By (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20090069836A1 (en) * 2007-08-17 2009-03-12 Micrus Endovascular Corporation Twisted primary coil for vascular therapy
WO2010120653A1 (en) * 2009-04-16 2010-10-21 Boston Scientific Scimed, Inc. Delivery wire for occlusive device delivery system and method of manufacture
US9241718B2 (en) 2012-11-16 2016-01-26 Sequent Medical, Inc. Delivery and detachment systems and methods for vascular implants

Families Citing this family (77)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6478773B1 (en) 1998-12-21 2002-11-12 Micrus Corporation Apparatus for deployment of micro-coil using a catheter
US7740637B2 (en) 2000-02-09 2010-06-22 Micrus Endovascular Corporation Apparatus and method for deployment of a therapeutic device using a catheter
US6835185B2 (en) 1998-12-21 2004-12-28 Micrus Corporation Intravascular device deployment mechanism incorporating mechanical detachment
DE60037025D1 (en) 1999-06-02 2007-12-20 Sethel Interventional Inc Intracorporal closure device
US6530934B1 (en) * 2000-06-06 2003-03-11 Sarcos Lc Embolic device composed of a linear sequence of miniature beads
US6743251B1 (en) 2000-11-15 2004-06-01 Scimed Life Systems, Inc. Implantable devices with polymeric detachment junction
US20020072791A1 (en) * 2000-12-07 2002-06-13 Eder Joseph C. Light-activated multi-point detachment mechanism
US6602269B2 (en) * 2001-03-30 2003-08-05 Scimed Life Systems Embolic devices capable of in-situ reinforcement
US6692510B2 (en) 2001-06-14 2004-02-17 Cordis Neurovascular, Inc. Aneurysm embolization device and deployment system
US20030204246A1 (en) * 2002-04-25 2003-10-30 Jack Chu Aneurysm treatment system and method
US8123774B2 (en) * 2003-03-20 2012-02-28 Boston Scientific Scimed, Inc. Piezoelectric vascular implant release device
US7789891B2 (en) 2003-09-23 2010-09-07 Boston Scientific Scimed, Inc. External activation of vaso-occlusive implants
US7763077B2 (en) 2003-12-24 2010-07-27 Biomerix Corporation Repair of spinal annular defects and annulo-nucleoplasty regeneration
US7641631B2 (en) * 2004-02-17 2010-01-05 Scimed Life Systems, Inc. Dilatation balloon having a valved opening and related catheters and methods
US20050267510A1 (en) * 2004-05-26 2005-12-01 Nasser Razack Device for the endovascular treatment of intracranial aneurysms
US20050278023A1 (en) * 2004-06-10 2005-12-15 Zwirkoski Paul A Method and apparatus for filling a cavity
US7918872B2 (en) 2004-07-30 2011-04-05 Codman & Shurtleff, Inc. Embolic device delivery system with retractable partially coiled-fiber release
US8845676B2 (en) 2004-09-22 2014-09-30 Micro Therapeutics Micro-spiral implantation device
EP1793744B1 (en) 2004-09-22 2008-12-17 Dendron GmbH Medical implant
KR101202369B1 (en) * 2004-10-29 2012-11-16 가부시키가이샤 가네카 메딕스 Medical wire
US8945024B2 (en) 2004-10-29 2015-02-03 Kaneka Medix Corporation Medical wire
US20060212113A1 (en) * 2005-02-24 2006-09-21 Shaolian Samuel M Externally adjustable endovascular graft implant
US8002789B2 (en) * 2005-05-31 2011-08-23 Stryker Corporation Stretch-resistant vaso-occlusive devices with flexible detachment junctions
US20070073334A1 (en) * 2005-09-29 2007-03-29 Kamal Ramzipoor Combined electrolytic and mechanical separation background
US9307996B2 (en) 2005-12-13 2016-04-12 DePuy Synthes Products, Inc. Detachment actuator for use with medical device deployment systems
US7942894B2 (en) 2006-01-31 2011-05-17 Codman & Shurtleff, Inc. Embolic device delivery system
US7344558B2 (en) * 2006-02-28 2008-03-18 Cordis Development Corporation Embolic device delivery system
WO2007114823A9 (en) * 2006-04-06 2008-10-09 Reva Medical Inc Embolic prosthesis for treatment of vascular aneurysm
CA2649702C (en) 2006-04-17 2014-12-09 Microtherapeutics, Inc. System and method for mechanically positioning intravascular implants
WO2007147127A3 (en) * 2006-06-15 2008-02-21 Cook Inc Methods, systems, and devices for the delivery of endoluminal prostheses
US8366720B2 (en) 2006-07-31 2013-02-05 Codman & Shurtleff, Inc. Interventional medical device system having an elongation retarding portion and method of using the same
US8062325B2 (en) 2006-07-31 2011-11-22 Codman & Shurtleff, Inc. Implantable medical device detachment system and methods of using the same
US8758407B2 (en) * 2006-12-21 2014-06-24 Warsaw Orthopedic, Inc. Methods for positioning a load-bearing orthopedic implant device in vivo
US8663328B2 (en) * 2006-12-21 2014-03-04 Warsaw Orthopedic, Inc. Methods for positioning a load-bearing component of an orthopedic implant device by inserting a malleable device that hardens in vivo
EP2124762B1 (en) 2007-03-13 2013-09-11 Covidien LP An implant including a coil and a stretch-resistant member
US20080306478A1 (en) * 2007-06-06 2008-12-11 Scott H. Bradshaw Method and Apparatus for Electrochemically Dissolving Selected Regions of Conducting Objects in Tissue
US20090112251A1 (en) * 2007-07-25 2009-04-30 Aga Medical Corporation Braided occlusion device having repeating expanded volume segments separated by articulation segments
US9034007B2 (en) 2007-09-21 2015-05-19 Insera Therapeutics, Inc. Distal embolic protection devices with a variable thickness microguidewire and methods for their use
US20090270901A1 (en) * 2007-10-30 2009-10-29 Boston Scientific Scimed, Inc. Degradable detachment mechanisms for implantable devices
EP2231030A4 (en) 2007-12-21 2016-12-21 Microvention Inc System and method for locating detachment zone of a detachable implant
EP2234562A4 (en) 2007-12-21 2016-12-21 Microvention Inc A system and method of detecting implant detachment
US20100082056A1 (en) * 2008-04-04 2010-04-01 Akshay Mavani Implantable fistula closure device
WO2009134337A1 (en) * 2008-05-01 2009-11-05 Aneuclose Llc Aneurysm occlusion device
EP2330985A4 (en) 2008-09-04 2015-11-18 Curaseal Inc Inflatable devices for enteric fistula treatment
DE102009025297A1 (en) * 2009-06-15 2010-12-16 Heraeus Medical Gmbh medical system
EP2461863B1 (en) * 2009-08-05 2016-07-27 Covidien LP Surgical wound dressing incorporating connected hydrogel beads having an embedded electrode therein
US8992563B2 (en) * 2009-11-02 2015-03-31 Boston Scientific Scimed, Inc. Delivery wire assembly for occlusive device delivery system
US20110106098A1 (en) * 2009-11-02 2011-05-05 Boston Scientific Scimed, Inc. Occlusive device delivery system
US9814562B2 (en) 2009-11-09 2017-11-14 Covidien Lp Interference-relief type delivery detachment systems
US20110184454A1 (en) * 2010-01-27 2011-07-28 Penumbra, Inc. Embolic implants
CA2795740C (en) 2010-04-14 2018-03-13 Microvention, Inc. Implant delivery device
US8322365B2 (en) 2010-08-17 2012-12-04 Codman & Shurtleff, Inc. Implantable adjustable valve
US9149615B2 (en) 2010-08-17 2015-10-06 DePuy Synthes Products, Inc. Method and tools for implanted device
JP6122424B2 (en) 2011-06-16 2017-04-26 キュラシール インコーポレイテッド Devices and related methods for fistula treatment
US9131941B2 (en) 2011-06-17 2015-09-15 Curaseal Inc. Fistula treatment devices and methods
US20130158510A1 (en) * 2011-06-30 2013-06-20 Incube Labs, Llc System and method for treatment of hemorrhagic stroke
US9579104B2 (en) 2011-11-30 2017-02-28 Covidien Lp Positioning and detaching implants
US9011480B2 (en) 2012-01-20 2015-04-21 Covidien Lp Aneurysm treatment coils
US9687245B2 (en) 2012-03-23 2017-06-27 Covidien Lp Occlusive devices and methods of use
US9326774B2 (en) 2012-08-03 2016-05-03 Covidien Lp Device for implantation of medical devices
CN104918565B (en) * 2012-11-13 2018-04-27 柯惠有限合伙公司 Occlusion device
US9468443B2 (en) 2012-12-27 2016-10-18 Cook Medical Technologies Llc Occlusion balloon
US20140257320A1 (en) * 2013-03-11 2014-09-11 Microvention, Inc. Implantable Device With Adhesive Properties
WO2014159606A1 (en) * 2013-03-14 2014-10-02 Stryker Corporation Vaso-occlusive device delivery system
WO2014145012A3 (en) 2013-03-15 2015-03-26 Covidien Lp Delivery and detachment mechanisms for vascular implants
US9314324B2 (en) 2013-07-29 2016-04-19 Insera Therapeutics, Inc. Vascular treatment devices and methods
US8679150B1 (en) 2013-03-15 2014-03-25 Insera Therapeutics, Inc. Shape-set textile structure based mechanical thrombectomy methods
US8715315B1 (en) 2013-03-15 2014-05-06 Insera Therapeutics, Inc. Vascular treatment systems
US8715314B1 (en) 2013-03-15 2014-05-06 Insera Therapeutics, Inc. Vascular treatment measurement methods
US9808599B2 (en) 2013-12-20 2017-11-07 Microvention, Inc. Device delivery system
US9867622B2 (en) 2014-04-11 2018-01-16 Microvention, Inc. Implant delivery system
US9713475B2 (en) 2014-04-18 2017-07-25 Covidien Lp Embolic medical devices
US9808256B2 (en) 2014-08-08 2017-11-07 Covidien Lp Electrolytic detachment elements for implant delivery systems
US9814466B2 (en) 2014-08-08 2017-11-14 Covidien Lp Electrolytic and mechanical detachment for implant delivery systems
CN107205736A (en) 2015-01-20 2017-09-26 纽罗加米医药公司 Micrograft for the treatment of intracranial aneurysms and method for use
US9717503B2 (en) 2015-05-11 2017-08-01 Covidien Lp Electrolytic detachment for implant delivery systems
US20170367709A1 (en) * 2016-06-28 2017-12-28 Covidien Lp Implant detachment with thermal activation

Citations (74)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4364392A (en) * 1980-12-04 1982-12-21 Wisconsin Alumni Research Foundation Detachable balloon catheter
US4402319A (en) * 1977-09-14 1983-09-06 Kuraray Co., Ltd. Releasable balloon catheter
US4512338A (en) * 1983-01-25 1985-04-23 Balko Alexander B Process for restoring patency to body vessels
US4545367A (en) * 1982-07-16 1985-10-08 Cordis Corporation Detachable balloon catheter and method of use
US4551132A (en) * 1980-02-18 1985-11-05 Emil Pasztor Pharmaceutically acceptable silicon rubber and therapeutical set and the use thereof for surgical embolization
US4638803A (en) * 1982-09-30 1987-01-27 Rand Robert W Medical apparatus for inducing scar tissue formation in a body
USRE32348E (en) * 1976-04-29 1987-02-10 Miniature balloon catheter method and apparatus
US4795741A (en) * 1987-05-06 1989-01-03 Biomatrix, Inc. Compositions for therapeutic percutaneous embolization and the use thereof
US4819637A (en) * 1987-09-01 1989-04-11 Interventional Therapeutics Corporation System for artificial vessel embolization and devices for use therewith
US4994069A (en) * 1988-11-02 1991-02-19 Target Therapeutics Vaso-occlusion coil and method
US5108407A (en) * 1990-06-08 1992-04-28 Rush-Presbyterian St. Luke's Medical Center Method and apparatus for placement of an embolic coil
US5133731A (en) * 1990-11-09 1992-07-28 Catheter Research, Inc. Embolus supply system and method
US5163952A (en) * 1990-09-14 1992-11-17 Michael Froix Expandable polymeric stent with memory and delivery apparatus and method
US5217484A (en) * 1991-06-07 1993-06-08 Marks Michael P Retractable-wire catheter device and method
US5226911A (en) * 1991-10-02 1993-07-13 Target Therapeutics Vasoocclusion coil with attached fibrous element(s)
US5256146A (en) * 1991-10-11 1993-10-26 W. D. Ensminger Vascular catheterization system with catheter anchoring feature
US5258042A (en) * 1991-12-16 1993-11-02 Henry Ford Health System Intravascular hydrogel implant
US5304194A (en) * 1991-10-02 1994-04-19 Target Therapeutics Vasoocclusion coil with attached fibrous element(s)
US5312415A (en) * 1992-09-22 1994-05-17 Target Therapeutics, Inc. Assembly for placement of embolic coils using frictional placement
US5334210A (en) * 1993-04-09 1994-08-02 Cook Incorporated Vascular occlusion assembly
US5334201A (en) * 1993-03-12 1994-08-02 Cowan Kevin P Permanent stent made of a cross linkable material
US5350397A (en) * 1992-11-13 1994-09-27 Target Therapeutics, Inc. Axially detachable embolic coil assembly
US5382260A (en) * 1992-10-30 1995-01-17 Interventional Therapeutics Corp. Embolization device and apparatus including an introducer cartridge and method for delivering the same
US5382259A (en) * 1992-10-26 1995-01-17 Target Therapeutics, Inc. Vasoocclusion coil with attached tubular woven or braided fibrous covering
US5423849A (en) * 1993-01-15 1995-06-13 Target Therapeutics, Inc. Vasoocclusion device containing radiopaque fibers
US5423829A (en) * 1993-11-03 1995-06-13 Target Therapeutics, Inc. Electrolytically severable joint for endovascular embolic devices
US5423777A (en) * 1993-10-27 1995-06-13 Tajiri; Akira Punctum plug
US5443454A (en) * 1992-12-09 1995-08-22 Terumo Kabushiki Kaisha Catheter for embolectomy
US5443495A (en) * 1993-09-17 1995-08-22 Scimed Lifesystems Inc. Polymerization angioplasty balloon implant device
US5443478A (en) * 1992-09-02 1995-08-22 Board Of Regents, The University Of Texas System Multi-element intravascular occlusion device
US5469867A (en) * 1992-09-02 1995-11-28 Landec Corporation Cast-in place thermoplastic channel occluder
US5525334A (en) * 1994-06-03 1996-06-11 Japan As Represented By Director General Of Agency Of Industrial Science And Technology Method for vascular embolization
US5529653A (en) * 1993-03-22 1996-06-25 Industrial Research B.V. Expandable hollow sleeve for the local support and/or reinforcement of a body vessel, and method for the fabrication thereof
US5536274A (en) * 1991-02-15 1996-07-16 pfm Produkterfur Die Medizin Spiral implant for organ pathways
US5578074A (en) * 1994-12-22 1996-11-26 Target Therapeutics, Inc. Implant delivery method and assembly
US5580568A (en) * 1995-07-27 1996-12-03 Micro Therapeutics, Inc. Cellulose diacetate compositions for use in embolizing blood vessels
US5582619A (en) * 1995-06-30 1996-12-10 Target Therapeutics, Inc. Stretch resistant vaso-occlusive coils
US5601600A (en) * 1995-09-08 1997-02-11 Conceptus, Inc. Endoluminal coil delivery system having a mechanical release mechanism
US5612050A (en) * 1993-03-23 1997-03-18 Focal, Inc. Apparatus and method for local application of polymeric material to tissue
US5614204A (en) * 1995-01-23 1997-03-25 The Regents Of The University Of California Angiographic vascular occlusion agents and a method for hemostatic occlusion
US5624885A (en) * 1991-07-16 1997-04-29 Sumitomo Electric Industries, Ltd. Josephson junction device of oxide superconductor and process for preparing the same
US5624481A (en) * 1994-06-01 1997-04-29 Wacker-Chemie Gmbh Process for the water-repellent impregnation of plaster
US5637938A (en) * 1994-08-16 1997-06-10 Whirlpool Corporation Tuned dynamic vibration absorber
US5645558A (en) * 1995-04-20 1997-07-08 Medical University Of South Carolina Anatomically shaped vasoocclusive device and method of making the same
US5658308A (en) * 1995-12-04 1997-08-19 Target Therapeutics, Inc. Bioactive occlusion coil
US5667767A (en) * 1995-07-27 1997-09-16 Micro Therapeutics, Inc. Compositions for use in embolizing blood vessels
US5669931A (en) * 1995-03-30 1997-09-23 Target Therapeutics, Inc. Liquid coils with secondary shape
US5690671A (en) * 1994-12-13 1997-11-25 Micro Interventional Systems, Inc. Embolic elements and methods and apparatus for their delivery
US5690667A (en) * 1996-09-26 1997-11-25 Target Therapeutics Vasoocclusion coil having a polymer tip
US5700258A (en) * 1994-06-24 1997-12-23 Target Therapeutics, Inc. Complex coils having fibered centers
US5702361A (en) * 1996-01-31 1997-12-30 Micro Therapeutics, Inc. Method for embolizing blood vessels
US5718711A (en) * 1992-11-18 1998-02-17 Target Therapeutics, Inc. Ultrasoft embolism devices and process for using them
US5722989A (en) * 1995-05-22 1998-03-03 The Regents Of The University Of California Microminiaturized minimally invasive intravascular micro-mechanical systems powered and controlled via fiber-optic cable
US5725568A (en) * 1995-06-27 1998-03-10 Scimed Life Systems, Inc. Method and device for recanalizing and grafting arteries
US5733329A (en) * 1996-12-30 1998-03-31 Target Therapeutics, Inc. Vaso-occlusive coil with conical end
US5743905A (en) * 1995-07-07 1998-04-28 Target Therapeutics, Inc. Partially insulated occlusion device
US5749891A (en) * 1995-06-06 1998-05-12 Target Therapeutics, Inc. Multiple layered vaso-occlusive coils
US5749894A (en) * 1996-01-18 1998-05-12 Target Therapeutics, Inc. Aneurysm closure method
US5759161A (en) * 1994-03-31 1998-06-02 Kaneka Medix Corporation Medical wire and method for leaving implanted devices
US5766204A (en) * 1995-06-07 1998-06-16 Metastent Incorporated Curable fiber composite stent and delivery system
US5792154A (en) * 1996-04-10 1998-08-11 Target Therapeutics, Inc. Soft-ended fibered micro vaso-occlusive devices
US5800454A (en) * 1997-03-17 1998-09-01 Sarcos, Inc. Catheter deliverable coiled wire thromboginic apparatus and method
US5814062A (en) * 1994-12-22 1998-09-29 Target Therapeutics, Inc. Implant delivery assembly with expandable coupling/decoupling mechanism
US5823198A (en) * 1996-07-31 1998-10-20 Micro Therapeutics, Inc. Method and apparatus for intravasculer embolization
US5830230A (en) * 1997-03-07 1998-11-03 Micro Therapeutics, Inc. Method of intracranial vascular embolotherapy using self anchoring coils
US5830178A (en) * 1996-10-11 1998-11-03 Micro Therapeutics, Inc. Methods for embolizing vascular sites with an emboilizing composition comprising dimethylsulfoxide
US5846210A (en) * 1996-09-20 1998-12-08 Kaneka Medix Corporation Medical wire having implanted device and method for using the same
US5851206A (en) * 1990-03-13 1998-12-22 The Regents Of The University Of California Method and apparatus for endovascular thermal thrombosis and thermal cancer treatment
US5902254A (en) * 1996-07-29 1999-05-11 The Nemours Foundation Cathether guidewire
US5941888A (en) * 1998-02-18 1999-08-24 Target Therapeutics, Inc. Vaso-occlusive member assembly with multiple detaching points
US6015424A (en) * 1998-04-28 2000-01-18 Microvention, Inc. Apparatus and method for vascular embolization
US6371979B1 (en) * 1993-01-27 2002-04-16 Intratherapeutics, Inc. Stent delivery system
US6375668B1 (en) * 1999-06-02 2002-04-23 Hanson S. Gifford Devices and methods for treating vascular malformations
US6383204B1 (en) * 1998-12-15 2002-05-07 Micrus Corporation Variable stiffness coil for vasoocclusive devices

Family Cites Families (51)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4346392A (en) * 1979-04-12 1982-08-24 Mutoh Industry Ltd. Plotting head for use in drawing machine
JPS6030225B2 (en) 1979-09-14 1985-07-15 Kuraray Co
USRE32248E (en) * 1981-03-19 1986-09-16 Twb-Pressteile Gmbh Grate for drainage ducts
US4735201A (en) * 1986-01-30 1988-04-05 The Beth Israel Hospital Association Optical fiber with detachable metallic tip for intravascular laser coagulation of arteries, veins, aneurysms, vascular malformations and arteriovenous fistulas
JPH0410831B2 (en) * 1988-03-18 1992-02-26
JPH0510954B2 (en) 1988-03-18 1993-02-12 Tokai Rika Denki Seisakusho Kk
US5569245A (en) * 1990-03-13 1996-10-29 The Regents Of The University Of California Detachable endovascular occlusion device activated by alternating electric current
US5976131A (en) 1990-03-13 1999-11-02 The Regents Of The University At California Detachable endovascular occlusion device activated by alternating electric current
US5122136A (en) * 1990-03-13 1992-06-16 The Regents Of The University Of California Endovascular electrolytically detachable guidewire tip for the electroformation of thrombus in arteries, veins, aneurysms, vascular malformations and arteriovenous fistulas
US6425893B1 (en) * 1990-03-13 2002-07-30 The Regents Of The University Of California Method and apparatus for fast electrolytic detachment of an implant
US5354295A (en) * 1990-03-13 1994-10-11 Target Therapeutics, Inc. In an endovascular electrolytically detachable wire and tip for the formation of thrombus in arteries, veins, aneurysms, vascular malformations and arteriovenous fistulas
JP3356447B2 (en) * 1991-10-16 2002-12-16 テルモ株式会社 Vascular lesions embolic material consisting of dried polymer gel
US5250071A (en) * 1992-09-22 1993-10-05 Target Therapeutics, Inc. Detachable embolic coil assembly using interlocking clasps and method of use
US5800453A (en) * 1993-04-19 1998-09-01 Target Therapeutics, Inc. Detachable embolic coil assembly using interlocking hooks and slots
US5498227A (en) * 1993-09-15 1996-03-12 Mawad; Michel E. Retrievable, shielded radiotherapy implant
CN1054418C (en) 1993-09-25 2000-07-12 Ksb股份公司 Turbo-machine with reduced attrition
US5624449A (en) * 1993-11-03 1997-04-29 Target Therapeutics Electrolytically severable joint for endovascular embolic devices
CA2162881C (en) 1994-04-07 2006-03-28 Arieh Sher Device for removal of intraluminal occlusions
EP0677817B1 (en) 1994-04-15 2000-11-08 Canon Kabushiki Kaisha Page segmentation and character recognition system
US5725546A (en) 1994-06-24 1998-03-10 Target Therapeutics, Inc. Detachable microcoil delivery catheter
US5522836A (en) 1994-06-27 1996-06-04 Target Therapeutics, Inc. Electrolytically severable coil assembly with movable detachment point
JPH10504738A (en) 1994-07-08 1998-05-12 マイクロベナ コーポレイション Forming method and vascular embolization device of the medical device
NL9401723A (en) 1994-10-18 1996-06-03 Gastec Nv Gas-fired dryer.
US5634936A (en) * 1995-02-06 1997-06-03 Scimed Life Systems, Inc. Device for closing a septal defect
US5639277A (en) * 1995-04-28 1997-06-17 Target Therapeutics, Inc. Embolic coils with offset helical and twisted helical shapes
US6312407B1 (en) 1995-06-05 2001-11-06 Medtronic Percusurge, Inc. Occlusion of a vessel
US5624461A (en) * 1995-06-06 1997-04-29 Target Therapeutics, Inc. Three dimensional in-filling vaso-occlusive coils
US6705323B1 (en) * 1995-06-07 2004-03-16 Conceptus, Inc. Contraceptive transcervical fallopian tube occlusion devices and methods
US6013084A (en) * 1995-06-30 2000-01-11 Target Therapeutics, Inc. Stretch resistant vaso-occlusive coils (II)
US6270495B1 (en) 1996-02-22 2001-08-07 Radiotherapeutics Corporation Method and device for enhancing vessel occlusion
JP3784112B2 (en) * 1996-08-15 2006-06-07 株式会社カネカメディックス Coiled embolic material
US5964797A (en) * 1996-08-30 1999-10-12 Target Therapeutics, Inc. Electrolytically deployable braided vaso-occlusion device
US5846247A (en) * 1996-11-15 1998-12-08 Unsworth; John D. Shape memory tubular deployment system
US5911737A (en) * 1997-02-28 1999-06-15 The Regents Of The University Of California Microfabricated therapeutic actuators
US5944733A (en) * 1997-07-14 1999-08-31 Target Therapeutics, Inc. Controlled detachable vasoocclusive member using mechanical junction and friction-enhancing member
US5984929A (en) * 1997-08-29 1999-11-16 Target Therapeutics, Inc. Fast detaching electronically isolated implant
JP4130234B2 (en) 1997-10-30 2008-08-06 株式会社カネカメディックス Implanted device arranged for medical devices
US6159165A (en) 1997-12-05 2000-12-12 Micrus Corporation Three dimensional spherical micro-coils manufactured from radiopaque nickel-titanium microstrand
US5935145A (en) 1998-02-13 1999-08-10 Target Therapeutics, Inc. Vaso-occlusive device with attached polymeric materials
US6293960B1 (en) * 1998-05-22 2001-09-25 Micrus Corporation Catheter with shape memory polymer distal tip for deployment of therapeutic devices
US6224610B1 (en) 1998-08-31 2001-05-01 Micrus Corporation Shape memory polymer intravascular delivery system with heat transfer medium
US6277126B1 (en) * 1998-10-05 2001-08-21 Cordis Neurovascular Inc. Heated vascular occlusion coil development system
US6296622B1 (en) * 1998-12-21 2001-10-02 Micrus Corporation Endoluminal device delivery system using axially recovering shape memory material
US6478773B1 (en) 1998-12-21 2002-11-12 Micrus Corporation Apparatus for deployment of micro-coil using a catheter
US6086599A (en) * 1999-02-08 2000-07-11 The Regents Of The University Of California Micro devices using shape memory polymer patches for mated connections
US6221066B1 (en) 1999-03-09 2001-04-24 Micrus Corporation Shape memory segmented detachable coil
WO2000066211A1 (en) * 1999-04-30 2000-11-09 Usaminanotechnology, Inc. Catheter and guide wire
DE60037025D1 (en) * 1999-06-02 2007-12-20 Sethel Interventional Inc Intracorporal closure device
US6238403B1 (en) * 1999-10-04 2001-05-29 Microvention, Inc. Filamentous embolic device with expansible elements
US7033374B2 (en) * 2000-09-26 2006-04-25 Microvention, Inc. Microcoil vaso-occlusive device with multi-axis secondary configuration
US6602269B2 (en) * 2001-03-30 2003-08-05 Scimed Life Systems Embolic devices capable of in-situ reinforcement

Patent Citations (78)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
USRE32348E (en) * 1976-04-29 1987-02-10 Miniature balloon catheter method and apparatus
US4402319A (en) * 1977-09-14 1983-09-06 Kuraray Co., Ltd. Releasable balloon catheter
US4551132A (en) * 1980-02-18 1985-11-05 Emil Pasztor Pharmaceutically acceptable silicon rubber and therapeutical set and the use thereof for surgical embolization
US4364392A (en) * 1980-12-04 1982-12-21 Wisconsin Alumni Research Foundation Detachable balloon catheter
US4545367A (en) * 1982-07-16 1985-10-08 Cordis Corporation Detachable balloon catheter and method of use
US4638803A (en) * 1982-09-30 1987-01-27 Rand Robert W Medical apparatus for inducing scar tissue formation in a body
US4512338A (en) * 1983-01-25 1985-04-23 Balko Alexander B Process for restoring patency to body vessels
US4795741A (en) * 1987-05-06 1989-01-03 Biomatrix, Inc. Compositions for therapeutic percutaneous embolization and the use thereof
US4819637A (en) * 1987-09-01 1989-04-11 Interventional Therapeutics Corporation System for artificial vessel embolization and devices for use therewith
US4994069A (en) * 1988-11-02 1991-02-19 Target Therapeutics Vaso-occlusion coil and method
US5851206A (en) * 1990-03-13 1998-12-22 The Regents Of The University Of California Method and apparatus for endovascular thermal thrombosis and thermal cancer treatment
US5108407A (en) * 1990-06-08 1992-04-28 Rush-Presbyterian St. Luke's Medical Center Method and apparatus for placement of an embolic coil
US5163952A (en) * 1990-09-14 1992-11-17 Michael Froix Expandable polymeric stent with memory and delivery apparatus and method
US5133731A (en) * 1990-11-09 1992-07-28 Catheter Research, Inc. Embolus supply system and method
US5536274A (en) * 1991-02-15 1996-07-16 pfm Produkterfur Die Medizin Spiral implant for organ pathways
US5217484A (en) * 1991-06-07 1993-06-08 Marks Michael P Retractable-wire catheter device and method
US5624885A (en) * 1991-07-16 1997-04-29 Sumitomo Electric Industries, Ltd. Josephson junction device of oxide superconductor and process for preparing the same
US5226911A (en) * 1991-10-02 1993-07-13 Target Therapeutics Vasoocclusion coil with attached fibrous element(s)
US5304194A (en) * 1991-10-02 1994-04-19 Target Therapeutics Vasoocclusion coil with attached fibrous element(s)
US5256146A (en) * 1991-10-11 1993-10-26 W. D. Ensminger Vascular catheterization system with catheter anchoring feature
US5258042A (en) * 1991-12-16 1993-11-02 Henry Ford Health System Intravascular hydrogel implant
US5443478A (en) * 1992-09-02 1995-08-22 Board Of Regents, The University Of Texas System Multi-element intravascular occlusion device
US5469867A (en) * 1992-09-02 1995-11-28 Landec Corporation Cast-in place thermoplastic channel occluder
US5312415A (en) * 1992-09-22 1994-05-17 Target Therapeutics, Inc. Assembly for placement of embolic coils using frictional placement
US5382259A (en) * 1992-10-26 1995-01-17 Target Therapeutics, Inc. Vasoocclusion coil with attached tubular woven or braided fibrous covering
US5476472A (en) * 1992-10-30 1995-12-19 Interventional Therapeutics Corporation Embolization device and apparatus including an introducer cartridge and a delivery catheter and method for delivering the embolization device
US5382260A (en) * 1992-10-30 1995-01-17 Interventional Therapeutics Corp. Embolization device and apparatus including an introducer cartridge and method for delivering the same
US5350397A (en) * 1992-11-13 1994-09-27 Target Therapeutics, Inc. Axially detachable embolic coil assembly
US5718711A (en) * 1992-11-18 1998-02-17 Target Therapeutics, Inc. Ultrasoft embolism devices and process for using them
US5443454A (en) * 1992-12-09 1995-08-22 Terumo Kabushiki Kaisha Catheter for embolectomy
US5423849A (en) * 1993-01-15 1995-06-13 Target Therapeutics, Inc. Vasoocclusion device containing radiopaque fibers
US6371979B1 (en) * 1993-01-27 2002-04-16 Intratherapeutics, Inc. Stent delivery system
US5334201A (en) * 1993-03-12 1994-08-02 Cowan Kevin P Permanent stent made of a cross linkable material
US5529653A (en) * 1993-03-22 1996-06-25 Industrial Research B.V. Expandable hollow sleeve for the local support and/or reinforcement of a body vessel, and method for the fabrication thereof
US5612050A (en) * 1993-03-23 1997-03-18 Focal, Inc. Apparatus and method for local application of polymeric material to tissue
US5334210A (en) * 1993-04-09 1994-08-02 Cook Incorporated Vascular occlusion assembly
US5443495A (en) * 1993-09-17 1995-08-22 Scimed Lifesystems Inc. Polymerization angioplasty balloon implant device
US5423777A (en) * 1993-10-27 1995-06-13 Tajiri; Akira Punctum plug
US5423829A (en) * 1993-11-03 1995-06-13 Target Therapeutics, Inc. Electrolytically severable joint for endovascular embolic devices
US5759161A (en) * 1994-03-31 1998-06-02 Kaneka Medix Corporation Medical wire and method for leaving implanted devices
US5624481A (en) * 1994-06-01 1997-04-29 Wacker-Chemie Gmbh Process for the water-repellent impregnation of plaster
US5525334A (en) * 1994-06-03 1996-06-11 Japan As Represented By Director General Of Agency Of Industrial Science And Technology Method for vascular embolization
US5700258A (en) * 1994-06-24 1997-12-23 Target Therapeutics, Inc. Complex coils having fibered centers
US5637938A (en) * 1994-08-16 1997-06-10 Whirlpool Corporation Tuned dynamic vibration absorber
US5690671A (en) * 1994-12-13 1997-11-25 Micro Interventional Systems, Inc. Embolic elements and methods and apparatus for their delivery
US5578074A (en) * 1994-12-22 1996-11-26 Target Therapeutics, Inc. Implant delivery method and assembly
US5814062A (en) * 1994-12-22 1998-09-29 Target Therapeutics, Inc. Implant delivery assembly with expandable coupling/decoupling mechanism
US5614204A (en) * 1995-01-23 1997-03-25 The Regents Of The University Of California Angiographic vascular occlusion agents and a method for hemostatic occlusion
US5669931A (en) * 1995-03-30 1997-09-23 Target Therapeutics, Inc. Liquid coils with secondary shape
US5766219A (en) * 1995-04-20 1998-06-16 Musc Foundation For Research Development Anatomically shaped vasoocclusive device and method for deploying same
US5645558A (en) * 1995-04-20 1997-07-08 Medical University Of South Carolina Anatomically shaped vasoocclusive device and method of making the same
US5722989A (en) * 1995-05-22 1998-03-03 The Regents Of The University Of California Microminiaturized minimally invasive intravascular micro-mechanical systems powered and controlled via fiber-optic cable
US5749891A (en) * 1995-06-06 1998-05-12 Target Therapeutics, Inc. Multiple layered vaso-occlusive coils
US5766204A (en) * 1995-06-07 1998-06-16 Metastent Incorporated Curable fiber composite stent and delivery system
US5725568A (en) * 1995-06-27 1998-03-10 Scimed Life Systems, Inc. Method and device for recanalizing and grafting arteries
US5582619A (en) * 1995-06-30 1996-12-10 Target Therapeutics, Inc. Stretch resistant vaso-occlusive coils
US5743905A (en) * 1995-07-07 1998-04-28 Target Therapeutics, Inc. Partially insulated occlusion device
US5851508A (en) * 1995-07-27 1998-12-22 Microtherapeutics, Inc. Compositions for use in embolizing blood vessels
US5667767A (en) * 1995-07-27 1997-09-16 Micro Therapeutics, Inc. Compositions for use in embolizing blood vessels
US5580568A (en) * 1995-07-27 1996-12-03 Micro Therapeutics, Inc. Cellulose diacetate compositions for use in embolizing blood vessels
US5601600A (en) * 1995-09-08 1997-02-11 Conceptus, Inc. Endoluminal coil delivery system having a mechanical release mechanism
US5658308A (en) * 1995-12-04 1997-08-19 Target Therapeutics, Inc. Bioactive occlusion coil
US5749894A (en) * 1996-01-18 1998-05-12 Target Therapeutics, Inc. Aneurysm closure method
US5702361A (en) * 1996-01-31 1997-12-30 Micro Therapeutics, Inc. Method for embolizing blood vessels
US5792154A (en) * 1996-04-10 1998-08-11 Target Therapeutics, Inc. Soft-ended fibered micro vaso-occlusive devices
US5902254A (en) * 1996-07-29 1999-05-11 The Nemours Foundation Cathether guidewire
US5823198A (en) * 1996-07-31 1998-10-20 Micro Therapeutics, Inc. Method and apparatus for intravasculer embolization
US5846210A (en) * 1996-09-20 1998-12-08 Kaneka Medix Corporation Medical wire having implanted device and method for using the same
US5690667A (en) * 1996-09-26 1997-11-25 Target Therapeutics Vasoocclusion coil having a polymer tip
US5830178A (en) * 1996-10-11 1998-11-03 Micro Therapeutics, Inc. Methods for embolizing vascular sites with an emboilizing composition comprising dimethylsulfoxide
US5733329A (en) * 1996-12-30 1998-03-31 Target Therapeutics, Inc. Vaso-occlusive coil with conical end
US5830230A (en) * 1997-03-07 1998-11-03 Micro Therapeutics, Inc. Method of intracranial vascular embolotherapy using self anchoring coils
US5800454A (en) * 1997-03-17 1998-09-01 Sarcos, Inc. Catheter deliverable coiled wire thromboginic apparatus and method
US5941888A (en) * 1998-02-18 1999-08-24 Target Therapeutics, Inc. Vaso-occlusive member assembly with multiple detaching points
US6015424A (en) * 1998-04-28 2000-01-18 Microvention, Inc. Apparatus and method for vascular embolization
US6375669B1 (en) * 1998-04-28 2002-04-23 Microvention, Inc. Apparatus and method for vascular embolization
US6383204B1 (en) * 1998-12-15 2002-05-07 Micrus Corporation Variable stiffness coil for vasoocclusive devices
US6375668B1 (en) * 1999-06-02 2002-04-23 Hanson S. Gifford Devices and methods for treating vascular malformations

Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20090069836A1 (en) * 2007-08-17 2009-03-12 Micrus Endovascular Corporation Twisted primary coil for vascular therapy
US8870908B2 (en) * 2007-08-17 2014-10-28 DePuy Synthes Products, LLC Twisted primary coil for vascular therapy
WO2010120653A1 (en) * 2009-04-16 2010-10-21 Boston Scientific Scimed, Inc. Delivery wire for occlusive device delivery system and method of manufacture
US20100268251A1 (en) * 2009-04-16 2010-10-21 Boston Scientific Scimed, Inc. Delivery wire for occlusive device delivery system and method of manufacture
US9241718B2 (en) 2012-11-16 2016-01-26 Sequent Medical, Inc. Delivery and detachment systems and methods for vascular implants

Also Published As

Publication number Publication date Type
US20020099408A1 (en) 2002-07-25 application
EP1200012B1 (en) 2007-11-07 grant
US9788840B2 (en) 2017-10-17 grant
EP1992308A2 (en) 2008-11-19 application
WO2000072781A3 (en) 2001-03-01 application
DE60037025T2 (en) 2008-09-11 grant
DE60037025D1 (en) 2007-12-20 grant
ES2299426T3 (en) 2008-06-01 grant
EP1992308B1 (en) 2015-10-28 grant
EP1992308A3 (en) 2009-12-02 application
EP1867300A3 (en) 2008-02-27 application
US20060271099A1 (en) 2006-11-30 application
US20060079929A1 (en) 2006-04-13 application
US20150173771A1 (en) 2015-06-25 application
EP1867300A2 (en) 2007-12-19 application
WO2000072781A2 (en) 2000-12-07 application
US20090076540A1 (en) 2009-03-19 application
ES2555961T3 (en) 2016-01-11 grant
EP2319455A3 (en) 2012-04-18 application
EP1200012A2 (en) 2002-05-02 application
EP2319455A2 (en) 2011-05-11 application
US20060265001A1 (en) 2006-11-23 application
US9526505B2 (en) 2016-12-27 grant
US8932317B2 (en) 2015-01-13 grant

Similar Documents

Publication Publication Date Title
US5980514A (en) Aneurysm closure device assembly
US6958061B2 (en) Microspheres with sacrificial coatings for vaso-occlusive systems
US6224610B1 (en) Shape memory polymer intravascular delivery system with heat transfer medium
US6994711B2 (en) Small diameter embolic coil hydraulic deployment system
US5527338A (en) Intravascular device
US7303571B2 (en) Methods and apparatus for blocking flow through blood vessels
US5814062A (en) Implant delivery assembly with expandable coupling/decoupling mechanism
US6855153B2 (en) Embolic balloon
US6183491B1 (en) Embolic coil deployment system with improved embolic coil
US20080281350A1 (en) Aneurysm Occlusion Devices
US6093199A (en) Intra-luminal device for treatment of body cavities and lumens and method of use
US7918872B2 (en) Embolic device delivery system with retractable partially coiled-fiber release
US20040034363A1 (en) Stretch resistant therapeutic device
US20120283768A1 (en) Method and apparatus for the treatment of large and giant vascular defects
US6254612B1 (en) Hydraulic stent deployment system
US6293960B1 (en) Catheter with shape memory polymer distal tip for deployment of therapeutic devices
US6979344B2 (en) Foam matrix embolization device
US6497671B2 (en) Coated superelastic stent
US5443478A (en) Multi-element intravascular occlusion device
US20040153025A1 (en) Systems and methods of de-endothelialization
US6511468B1 (en) Device and method for controlling injection of liquid embolic composition
US6616617B1 (en) Vasoocclusive device for treatment of aneurysms
US20040153120A1 (en) Systems and methods of de-endothelialization
US7632291B2 (en) Inflatable implant
US20080306503A1 (en) Mechanically detachable vaso-occlusive device

Legal Events

Date Code Title Description
AS Assignment

Owner name: MICROTRANSFORM, INC., CALIFORNIA

Free format text: MERGER;ASSIGNOR:SETHEL INVERVENTIONAL, INC.;REEL/FRAME:020145/0203

Effective date: 20071109

AS Assignment

Owner name: MARKS, MICHAEL P., CALIFORNIA

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:MICROTRANSFORM, INC.;REEL/FRAME:042393/0134

Effective date: 20170513