US20050192655A1 - Method of forming a lead - Google Patents
Method of forming a lead Download PDFInfo
- Publication number
- US20050192655A1 US20050192655A1 US11/078,788 US7878805A US2005192655A1 US 20050192655 A1 US20050192655 A1 US 20050192655A1 US 7878805 A US7878805 A US 7878805A US 2005192655 A1 US2005192655 A1 US 2005192655A1
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- United States
- Prior art keywords
- lead
- conductor
- electrodes
- insulative material
- accordance
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
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- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01R—ELECTRICALLY-CONDUCTIVE CONNECTIONS; STRUCTURAL ASSOCIATIONS OF A PLURALITY OF MUTUALLY-INSULATED ELECTRICAL CONNECTING ELEMENTS; COUPLING DEVICES; CURRENT COLLECTORS
- H01R43/00—Apparatus or processes specially adapted for manufacturing, assembling, maintaining, or repairing of line connectors or current collectors or for joining electric conductors
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/04—Electrodes
- A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/04—Electrodes
- A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
- A61N1/0551—Spinal or peripheral nerve electrodes
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/04—Electrodes
- A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
- A61N1/056—Transvascular endocardial electrode systems
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- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T29/00—Metal working
- Y10T29/49—Method of mechanical manufacture
- Y10T29/49002—Electrical device making
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T29/00—Metal working
- Y10T29/49—Method of mechanical manufacture
- Y10T29/49002—Electrical device making
- Y10T29/49117—Conductor or circuit manufacturing
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T29/00—Metal working
- Y10T29/49—Method of mechanical manufacture
- Y10T29/49002—Electrical device making
- Y10T29/49117—Conductor or circuit manufacturing
- Y10T29/49174—Assembling terminal to elongated conductor
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T29/00—Metal working
- Y10T29/49—Method of mechanical manufacture
- Y10T29/49002—Electrical device making
- Y10T29/49117—Conductor or circuit manufacturing
- Y10T29/49174—Assembling terminal to elongated conductor
- Y10T29/49176—Assembling terminal to elongated conductor with molding of electrically insulating material
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T29/00—Metal working
- Y10T29/49—Method of mechanical manufacture
- Y10T29/49002—Electrical device making
- Y10T29/49117—Conductor or circuit manufacturing
- Y10T29/49204—Contact or terminal manufacturing
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T29/00—Metal working
- Y10T29/49—Method of mechanical manufacture
- Y10T29/49002—Electrical device making
- Y10T29/49117—Conductor or circuit manufacturing
- Y10T29/49204—Contact or terminal manufacturing
- Y10T29/49208—Contact or terminal manufacturing by assembling plural parts
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T29/00—Metal working
- Y10T29/49—Method of mechanical manufacture
- Y10T29/49002—Electrical device making
- Y10T29/49117—Conductor or circuit manufacturing
- Y10T29/49204—Contact or terminal manufacturing
- Y10T29/49208—Contact or terminal manufacturing by assembling plural parts
- Y10T29/4922—Contact or terminal manufacturing by assembling plural parts with molding of insulation
Definitions
- the present invention relates to a lead, and in particular, to an implantable lead and a method of manufacturing such lead.
- Implantable leads having ring electrodes can be used in a variety of applications, including delivery of electrical stimulation to surrounding tissue, neural or otherwise, as well as measuring electrical energy produced by such tissue. Whether serving in a stimulation capacity or a sensing capacity, such leads are commonly implanted along peripheral nerves, within the epidural or the intrathecal spaces of the spinal column, about the heart, and in the brain.
- implantable leads include flexibility, strength, and durability. The extent of such qualities, of course, is dependent upon the nature of the use, for example, temporary or permanent implantation. While material selection and certain construction techniques can be tailored to assist in meeting these prescribed characteristics, an overriding consideration in the design of such leads is achieving at least an isodiametric stimulation/pacing portion thereof.
- an isodiametric lead can reduce the potential for damage to the lead during insertion (for example, when a lead is passed through an insertion needle to reach a patient epidural space) and/or placement, improve the ability of the lead to pass through tissue or a vascular system, and is more resistant to being immobilized by tissue growth at a permanent implantation site.
- Differing techniques have been used to produce isodiametric leads.
- One such technique concerns adhering a plurality of elements (i.e., conductive electrodes, conductive terminals, and spacing insulative tubing material) to produce a generally integral body.
- Tubing material separates a stimulation/sensing portion (i.e., alternating insulative tubing material and electrodes) from a terminal portion (i.e., alternating insulative tubing material and terminals).
- the electrodes, terminals, and tubing are independently formed but are intended to be isodiametric. Understandably, dimension variances in any one element can result in a lead having a varying diameter.
- a composition for example, medical grade epoxy, is injected within an interior of the leads in and about the stimulation/sensing portions and the terminal portions. While this technique does typically effect stabilization and strengthening of these critical regions, the end result can also be that these regions are too rigid and even brittle.
- a ring electrode(s) about an exterior surface of insulative tubing that forms the main body of the lead.
- the insulative tubing may be prepared to receive the electrode, for example, milled to remove an amount of material substantially equal to the material thickness of the ring electrode.
- the insulative tubing may be unprepared, for example, a ring electrode is simply “crimped” to a diameter substantially equal to the otherwise unadulterated diameter of the tubing.
- a finished lead is still comprised of a plurality of independent components brought together in an effort to form an isodiametric cross-section.
- Element misalignment, inaccuracies in grinding, variances in electrode material thickness or individual element dimensions, or over/under-crimping could respectively result in at least undesirable variances in lead diameter.
- One aspect of the present invention is directed to an implantable lead including a lead body, having a distal end and a proximal end, whereas the lead body is formed of a material having prescribed mechanical properties.
- a first region includes a plurality of electrodes.
- a first insulative material having mechanical properties consistent with the material of the lead body, separates adjacent electrodes.
- a second region includes at least one terminal.
- a second insulative material having mechanical properties consistent with the material of the lead body, separates adjacent terminals.
- a conductor couples each terminal to at least one corresponding electrode of the plurality of electrodes, wherein the conductor(s) extends along an interior passage defined by the lead body, first region, and second region.
- the interior passage of the first region is substantially filled with a third insulative material having mechanical properties consistent with the material of the lead body:
- Another aspect of the present invention concerns a method of forming a substantially isodiametric lead.
- such lead has a prescribed diameter and includes at least one electrode separated from at least one terminal by a lead body, wherein the at least one electrode is electrically coupled to the at least one terminal by a conductor passing through a passage defined by at least the lead body.
- the forming steps include assembling the at least one electrode and the at least one terminal relative to the lead body to form an assembly, including connecting the at least one electrode to the at least one terminal via the conductor.
- the assembly is subjected to an over-molding process that over molds the assembly with a first material to form an intermediate assembly. This first material is compatible with and has mechanical properties consistent with a material of the lead body.
- the intermediate assembly is processed to remove all material of the intermediate assembly in excess of the prescribed diameter.
- An object of the present invention is to avoid the shortcomings of known leads and manufacturing techniques for the same.
- Another object of the present invention is to provide a method of forming a lead having a true isodiametric body for at least the stimulation/sensing portion of the lead.
- Another object of the present invention is to provide a lead having a true isodiametric body for at least the stimulation/sensing portion of the lead.
- Another object of the present invention is to provide a lead having a low resistance from a terminal to a coupled electrode to reduce energy consumption during system operation.
- FIG. 1 is a perspective view of a multi-electrode lead in accordance with the present invention
- FIG. 2 is a plan view of another embodiment of a multi-electrode lead in accordance with the present invention.
- FIG. 3 is a sectional view of the lead of FIG. 2 , taken along line III-III;
- FIG. 4 is a perspective view of a preferred conductor
- FIG. 5 is a plan view of an assembly of elements on a mandrel used to form a lead in accordance with the present invention
- FIG. 6 is a sectional view of a transitional element
- FIG. 7 is a perspective view of an electrode spacer
- FIG. 8 is a perspective view of a terminal spacer
- FIG. 9 is a sectional view of a stylet guide
- FIG. 10 is a sectional view of a cap electrode
- FIG. 11 is a schematic representation of one embodiment of an assembly fixture used to assemble a lead in accordance with the present invention.
- FIG. 1 illustrates a preferred embodiment of multi-electrode lead 10 . While the leads illustrated and generally discussed here have eight electrodes, lead 10 of the present invention may be constructed having any number of electrodes (i.e., one or more):
- Lead 10 includes a proximal end 12 and a distal end 14 .
- the proximal end 12 includes a plurality of electrically conductive terminals 16
- the distal end 14 includes a plurality of electrically conductive electrodes 18 . While typically each terminal 16 is electrically connected to a single electrode 18 via a conductor 20 ( FIG. 3 ), a terminal 16 can be connected to two or more electrodes 18 .
- Terminals 16 and electrodes 18 are preferably formed of a non-corrosive, highly conductive material. Examples of such material include stainless steel, MP35N, platinum, and platinum alloys. In a preferred embodiment, terminals 16 and electrodes 18 are formed of a platinum-iridium alloy.
- body 22 Spanning between electrodes 18 of the distal end 14 and terminals 16 of the proximal end 12 , body 22 is formed from a medical grade, substantially inert material, for example, polyurethane, silicone, or the like. While the specific material used for body 22 is not critical to the present invention, body 22 must be non-reactive to the environment of the human body, provide a flexible and durable (i.e., fatigue resistant) exterior structure for the components of lead 10 , and insulate adjacent terminals 16 and/or electrodes 18 .
- a medical grade, substantially inert material for example, polyurethane, silicone, or the like. While the specific material used for body 22 is not critical to the present invention, body 22 must be non-reactive to the environment of the human body, provide a flexible and durable (i.e., fatigue resistant) exterior structure for the components of lead 10 , and insulate adjacent terminals 16 and/or electrodes 18 .
- body 22 substantially provides the exterior structure that contains the internalized elements of lead 10 .
- body 22 provides an enclosure for each conductor 20 that connects a terminal 16 with one or more electrodes 18 .
- Each conductor 20 is formed of a conductive material that exhibits the desired mechanical properties of low resistance, corrosion resistance, flexibility, and strength.
- a plurality of conductors 20 are required to fit within the interior of body 22 . Accordingly, the cross-sectional area of each conductor 20 is restricted.
- conductor 20 could be on the order of approximately 0.0065 inches.
- conductors 20 utilizes wires formed of multi-strands of drawn-filled tubes (DFT), as illustrated in FIG. 4 .
- DFT drawn-filled tubes
- Each strand is formed of a low resistance material 20 a and is encased in a high strength material 20 b (preferably, metal).
- a selected number of strands are wound and coated with an insulative material 20 c.
- insulative material 20 c protects the individual conductors 20 if body 22 were breached during use.
- Wire formed of multi-strands of drawn-filled tubes to form conductors 20 is available from Temp-Flex Cable, Inc. (City, State).
- conductors 20 formed of multi-strands of drawn-filled tubes provide a low resistance alternative to other conventional materials.
- a stranded wire, or even coiled wire, of approximately 60 cm and formed of MP35N or stainless steel or the like would have a measured resistance in excess of 30 ohms.
- a wire formed of multi-strands of drawn-filled tubes, as illustrated in FIG. 4 could have a resistance less than 4 ohms.
- each conductor 20 having a length equal to or less than 60 cm, has a resistance of less than 25 ohms.
- each conductor 20 having a length equal to or less than 60 cm, has a resistance equal to or less than 10 ohms. In a most preferred embodiment, each conductor 20 , having a length equal to or less than 60 cm, has a resistance of less than 4 ohms.
- body 22 can further encompass stylet tubing 24 ( FIG. 3 ).
- Stylet tubing 24 extends from the proximal end 12 to a point within a distal portion of lead 10 ; however, in a preferred embodiment, stylet tubing 24 extends to cap electrode 34 .
- stylet tubing 24 operatively receives stylet 100 for purposes of allowing better control over lead 10 during placement.
- the following example includes certain physical dimensions to illustrate the relationship between elements as well as effects of differing processes. Accordingly, the provided physical dimensions are used merely for example and shall not restrict the scope of the present invention.
- a lead in accordance with the present invention may have more than or less than eight electrodes and/or have a larger or smaller diameter than the following example and remain within the scope of this disclosure.
- stylet tubing 24 is positioned over mandrel 150 .
- Stylet tubing 24 has an outer diameter of approximately 0.02 inches.
- arranging and securing conductors 20 can be problematic when they are being arranged and secured about an element having the dimensions of stylet tubing 24 .
- FIG. 11 illustrates an example of a fixture 200 that can assist in this task.
- fixture 200 includes first rotary clamp 202 , iris 204 , iris 206 , second rotary clamp 208 , and clamp 210 .
- Rotary clamps 202 and 208 each include a corresponding plurality of conductor clamps 203 . While not required, it is preferred that the plurality of conductor clamps 203 of each rotary claim 202 and 208 be positioned within an arbitrary perimeter 205 , whereas perimeter 205 should be equal to or greater than a fully-opened inner diameter of either iris 204 or 206 .
- mandrel 150 passes through irises 204 and 206 and second rotary clamp 208 and is secured between clamps 202 and 210 .
- Each conductor 20 similarly passes through irises 204 and 206 and is secured between respective clamps 203 of rotary clamps 202 and 208 .
- Conductors 20 secured within fixture 200 are prepared for assembly in that a prescribed amount of insulative material 20 c is removed at or about the proximal and distal ends of each conductor 20 to expose conductive material 20 a and 20 b. As will be discussed later, this exposed conductive material 20 a and 20 b of the proximal and distal ends of each conductor 20 is eventually joined to an electrode 18 and a terminal 16 . Accordingly, the exposed conductive material 20 a and 20 b is arranged at differing positions relative to stylet tubing 24 to accommodate the serial arrangement of terminals 16 and electrodes 18 .
- rotary clamps 202 and 208 provide unobstructed access to the in-process lead 10 . Specifically, upon securing a single conductor 20 between opposing (or non-opposing) clamps 203 , the rotary clamps 202 and 210 are simply rotated to allow access to unoccupied clamps 203 .
- conductor(s) 20 When all of the conductors 20 are strung between claims 202 and 208 , irises 204 and 206 are actuated to close and draw conductor(s) 20 closely about the outer diameter of stylet tubing 24 . When conductor(s) 20 are resting against the outer diameter of stylet tubing 24 , conductor(s) 20 are secured in place. Conductor(s) 20 may be secured using adhesive and/or subjected to a force applied through use of a temporary or permanent restraint, for example, one or more crimped collars.
- FIG. 11 shows but one embodiment of fixture 200
- clamps 203 of each rotary clamp 202 and 208 could be moveable along respective radial paths (not shown) that would allow strung conductors 20 to be moved from a first position to a second position adjacent the exterior surface of stylet tubing 24 .
- conductors 20 could initially be secured to one end of stylet tubing 24 and only a single iris could be used to draw the unsecured portions of conductors 20 toward stylet tubing 24 .
- an operator could simply manipulate the conductor(s) 20 to manually position and secure them relative to stylet tubing 24 .
- transitional element 26 electrode(s) 18 , electrode spacer(s) 28 , outer tubing 23 , terminal spacer(s) 30 , terminal(s) 16 , and stylet guide 32 are positioned over, and concentrically arranged with, stylet tubing 24 .
- the arrangement of these elements is in accordance with that illustrated in FIG. 5 .
- Transitional element 26 is illustrated in FIG. 6 . As will be discussed later, transitional element 26 provides a platform to receive cap electrode 34 ( FIG. 10 ). Transitional element 26 further provides a durable guide 26 a to direct a distal end (not shown) of stylet 100 to cap electrode 34 via passage 26 b. Transitional element 26 is preferably formed of a conductive material, for example, the same material used to form electrodes 18 .
- Electrode spacer 28 is illustrated in FIG. 7 .
- terminal spacer 30 is illustrated in FIG. 8 .
- electrode spacer 28 and terminal spacer 30 accurately defines a space between adjacent electrodes 18 and terminals 16 , respectively.
- Electrode spacer 28 and terminal spacer 30 are preferably formed of the same material as outer tubing 23 .
- spacers 28 and 30 may be formed of a material that differs from that of outer tubing 23 ; provided however, any differing material used for electrode spacer 28 and/or terminal spacer 30 must be compatible with and possess largely the same mechanical properties (e.g., non-reactive to the environment of the human body, flexible and durable) as outer tubing 23 .
- spacers 28 , and 30 are formed of a polyurethane material, for example, Bionate 75D (Polymer Tech. Group, City, State). As is noted in FIG. 5 , spacers 28 and 30 should have an outer diameter greater than lead 10 .
- Outer tubing 23 separates electrodes 18 from terminals 16 .
- outer tubing 23 has a diameter substantially equal to a diameter of lead 10 .
- outer tubing 23 may have a diameter less than lead 10 , or a diameter greater than lead 10 .
- outer tubing 23 must have a wall thickness greater than a differential between a radius of lead 10 and a radius (to the outer diameter) of outer tubing 23 .
- outer tubing 23 has a nominal outer diameter of approximate 0.055 inches.
- Stylet guide 32 is illustrated in FIG. 9 .
- Stylet guide 32 provides an inlet to stylet tubing 24 .
- Stylet guide 32 is preferably formed of conductive material, for example, the same material used to form electrodes 18 .
- Stylet guide 32 , as well as terminals 16 , electrodes 18 , and transitional element 26 preferably each have an outer diameter equal to or greater than a nominal diameter of lead 10 . In a more preferred embodiment, these elements each have an outer diameter greater than a nominal diameter of lead 10 .
- terminals 16 and electrodes 18 are joined to their respective conductors 20 .
- each terminal 16 (and each electrode 18 ) is positioned relative to exposed conductive material 20 a and 20 b of a conductor 20 and is joined in a manner that facilitates a transfer of electrical energy, for example, resistance weld or laser weld.
- stylet guide 32 is secured to a proximal-most terminal 16
- transitional element 26 is secured to a distal-most electrode 18 .
- transitional element 26 and stylet guide 32 are formed a conductive material, these elements may be secured using a process consistent with that used to join terminals 16 and electrodes 18 with conductors 20 . Otherwise, transitional element 26 and stylet guide 32 can be joined using an adhesive, cement or the like.
- the completed assembly ( FIG. 5 ) is then over-molded, using well known injection molding techniques, using a material having mechanical properties consistent with a material(s) used to form outer tubing 23 , electrode spacer 28 , and terminal spacer 30 .
- the over-molding material and the material of outer tubing 23 , electrode spacer 28 , and terminal 28 are the same.
- Electrode spacers 28 and terminal spacers 30 are placed in a state of flow, which, at least in part, results in a filling of regions between terminals 16 /electrodes 18 and stylet guide 24 . Consequently, terminals 16 and electrodes 18 are partially surrounded (i.e., along an interior surface) and supported by a fused matrix of; material.
- electrode spacers 28 and terminal spacers 30 are formed of a material mechanically equivalent to that of body 22 /outer tubing 23 , the stimulation/sensing portion and terminal portion of lead 10 are stabilized and strengthened while also retaining their flexible properties.
- the over-molded assembly (not shown) is then subjected to a grinding process to remove all excess material.
- the over-molded assembly is subject to centerless grinding, wherein excessive material, including over-molded material, electrode material, terminal material, and the like, is removed.
- an isodiametric lead is obtained, which is further free of any gaps or voids between insulative material and conductive material that may otherwise exist in conventional devices.
- cap electrode 34 is affixed to transitional element 26 using conventional means, for example, resistance welding, laser welding, or the like.
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Abstract
An implantable, substantially isodiametric, low resistance implantable lead having at least one electrode positioned in a stimulation/sensing portion of the lead as well as a method of manufacturing the same. At least the stimulation/sensing portion is unitized through partially surrounding and supporting insulation and conductive element(s) of the stimulation/sensing portion with a fused matrix of material having mechanical properties consistent with a body of the lead.
Description
- This is a division of U.S. patent application Ser. No. 09/760,437, filed Jan. 12, 2001, pending, which is a division of U.S. patent application Ser. No. 09/299,702, filed Apr. 26, 1999, issued as U.S. Pat. No. 6,216,045.
- The present invention relates to a lead, and in particular, to an implantable lead and a method of manufacturing such lead.
- Implantable leads having ring electrodes can be used in a variety of applications, including delivery of electrical stimulation to surrounding tissue, neural or otherwise, as well as measuring electrical energy produced by such tissue. Whether serving in a stimulation capacity or a sensing capacity, such leads are commonly implanted along peripheral nerves, within the epidural or the intrathecal spaces of the spinal column, about the heart, and in the brain.
- Notwithstanding the application, the common requirements for such implantable leads include flexibility, strength, and durability. The extent of such qualities, of course, is dependent upon the nature of the use, for example, temporary or permanent implantation. While material selection and certain construction techniques can be tailored to assist in meeting these prescribed characteristics, an overriding consideration in the design of such leads is achieving at least an isodiametric stimulation/pacing portion thereof.
- The benefits of achieving desired levels of flexibility, strength, and durability are intuitive. The isodiametric characteristic is likely less obvious. Depending upon the application, an isodiametric lead can reduce the potential for damage to the lead during insertion (for example, when a lead is passed through an insertion needle to reach a patient epidural space) and/or placement, improve the ability of the lead to pass through tissue or a vascular system, and is more resistant to being immobilized by tissue growth at a permanent implantation site.
- Differing techniques have been used to produce isodiametric leads. One such technique concerns adhering a plurality of elements (i.e., conductive electrodes, conductive terminals, and spacing insulative tubing material) to produce a generally integral body. Tubing material separates a stimulation/sensing portion (i.e., alternating insulative tubing material and electrodes) from a terminal portion (i.e., alternating insulative tubing material and terminals). The electrodes, terminals, and tubing are independently formed but are intended to be isodiametric. Understandably, dimension variances in any one element can result in a lead having a varying diameter.
- Of further interest, to strengthen the plurality of element interfaces found in the stimulation/sensing portions and terminal portions of these leads, a composition, for example, medical grade epoxy, is injected within an interior of the leads in and about the stimulation/sensing portions and the terminal portions. While this technique does typically effect stabilization and strengthening of these critical regions, the end result can also be that these regions are too rigid and even brittle.
- Other techniques include applying a ring electrode(s) about an exterior surface of insulative tubing that forms the main body of the lead. The insulative tubing may be prepared to receive the electrode, for example, milled to remove an amount of material substantially equal to the material thickness of the ring electrode. Alternatively, the insulative tubing may be unprepared, for example, a ring electrode is simply “crimped” to a diameter substantially equal to the otherwise unadulterated diameter of the tubing.
- For all of the methods described above, a finished lead is still comprised of a plurality of independent components brought together in an effort to form an isodiametric cross-section. Element misalignment, inaccuracies in grinding, variances in electrode material thickness or individual element dimensions, or over/under-crimping could respectively result in at least undesirable variances in lead diameter.
- Accordingly, a need exists for a lead, as well as a method of fabricating such lead, that provides a requisite level of flexibility, strength, and durability, while further providing a true isodiametric body for at least the stimulation/sensing portion of the lead.
- One aspect of the present invention is directed to an implantable lead including a lead body, having a distal end and a proximal end, whereas the lead body is formed of a material having prescribed mechanical properties. Extending from the distal end of the lead body, a first region includes a plurality of electrodes. A first insulative material, having mechanical properties consistent with the material of the lead body, separates adjacent electrodes. Extending from the proximal end of the lead body, a second region includes at least one terminal. A second insulative material, having mechanical properties consistent with the material of the lead body, separates adjacent terminals. A conductor couples each terminal to at least one corresponding electrode of the plurality of electrodes, wherein the conductor(s) extends along an interior passage defined by the lead body, first region, and second region. In addition to the at least one conductor, the interior passage of the first region is substantially filled with a third insulative material having mechanical properties consistent with the material of the lead body:
- Another aspect of the present invention concerns a method of forming a substantially isodiametric lead. Specifically, such lead has a prescribed diameter and includes at least one electrode separated from at least one terminal by a lead body, wherein the at least one electrode is electrically coupled to the at least one terminal by a conductor passing through a passage defined by at least the lead body. The forming steps include assembling the at least one electrode and the at least one terminal relative to the lead body to form an assembly, including connecting the at least one electrode to the at least one terminal via the conductor. The assembly is subjected to an over-molding process that over molds the assembly with a first material to form an intermediate assembly. This first material is compatible with and has mechanical properties consistent with a material of the lead body. Ultimately, the intermediate assembly is processed to remove all material of the intermediate assembly in excess of the prescribed diameter.
- An object of the present invention is to avoid the shortcomings of known leads and manufacturing techniques for the same.
- Another object of the present invention is to provide a method of forming a lead having a true isodiametric body for at least the stimulation/sensing portion of the lead.
- Another object of the present invention is to provide a lead having a true isodiametric body for at least the stimulation/sensing portion of the lead.
- Another object of the present invention is to provide a lead having a low resistance from a terminal to a coupled electrode to reduce energy consumption during system operation.
- Other aspects, objects, and advantages of the present invention will be apparent to those of ordinary skill in the art having reference to the following Specification together with the provided drawings.
- In reference to the following figures, like reference numerals and letters indicate corresponding elements:
-
FIG. 1 is a perspective view of a multi-electrode lead in accordance with the present invention; -
FIG. 2 is a plan view of another embodiment of a multi-electrode lead in accordance with the present invention; -
FIG. 3 is a sectional view of the lead ofFIG. 2 , taken along line III-III; -
FIG. 4 is a perspective view of a preferred conductor; -
FIG. 5 is a plan view of an assembly of elements on a mandrel used to form a lead in accordance with the present invention; -
FIG. 6 is a sectional view of a transitional element; -
FIG. 7 is a perspective view of an electrode spacer; -
FIG. 8 is a perspective view of a terminal spacer; -
FIG. 9 is a sectional view of a stylet guide; -
FIG. 10 is a sectional view of a cap electrode; and -
FIG. 11 is a schematic representation of one embodiment of an assembly fixture used to assemble a lead in accordance with the present invention. - Various embodiments, including preferred embodiments, will now be described in detail below with reference to the drawings:
-
FIG. 1 illustrates a preferred embodiment ofmulti-electrode lead 10. While the leads illustrated and generally discussed here have eight electrodes, lead 10 of the present invention may be constructed having any number of electrodes (i.e., one or more): -
Lead 10 includes aproximal end 12 and adistal end 14. Theproximal end 12 includes a plurality of electricallyconductive terminals 16, and thedistal end 14 includes a plurality of electricallyconductive electrodes 18. While typically each terminal 16 is electrically connected to asingle electrode 18 via a conductor 20 (FIG. 3 ), a terminal 16 can be connected to two ormore electrodes 18. -
Terminals 16 andelectrodes 18 are preferably formed of a non-corrosive, highly conductive material. Examples of such material include stainless steel, MP35N, platinum, and platinum alloys. In a preferred embodiment,terminals 16 andelectrodes 18 are formed of a platinum-iridium alloy. - Spanning between
electrodes 18 of thedistal end 14 andterminals 16 of theproximal end 12,body 22 is formed from a medical grade, substantially inert material, for example, polyurethane, silicone, or the like. While the specific material used forbody 22 is not critical to the present invention,body 22 must be non-reactive to the environment of the human body, provide a flexible and durable (i.e., fatigue resistant) exterior structure for the components oflead 10, and insulateadjacent terminals 16 and/orelectrodes 18. - Serving as a sheath,
body 22 substantially provides the exterior structure that contains the internalized elements oflead 10. Specifically,body 22 provides an enclosure for eachconductor 20 that connects a terminal 16 with one ormore electrodes 18. Eachconductor 20 is formed of a conductive material that exhibits the desired mechanical properties of low resistance, corrosion resistance, flexibility, and strength. For consideration, however, it should be appreciated that in the context of amultiple electrode lead 10, a plurality ofconductors 20 are required to fit within the interior ofbody 22. Accordingly, the cross-sectional area of eachconductor 20 is restricted. As but one example, for a lead in accordance with the present invention that has an outer diameter of approximately 0.055 inches,conductor 20 could be on the order of approximately 0.0065 inches. - While stranded bundles of stainless steel, MP35N, platinum, platinum-iridium alloy, drawn-brazed silver (DBS) or the like can be used, the preferred embodiment of
conductors 20 utilizes wires formed of multi-strands of drawn-filled tubes (DFT), as illustrated inFIG. 4 . Each strand is formed of alow resistance material 20 a and is encased in ahigh strength material 20 b (preferably, metal). A selected number of strands (seven, for this example) are wound and coated with aninsulative material 20 c. With regard to the operating environment of the present invention,insulative material 20 c protects theindividual conductors 20 ifbody 22 were breached during use. Wire formed of multi-strands of drawn-filled tubes to formconductors 20, as discussed here, is available from Temp-Flex Cable, Inc. (City, State). - In addition to providing the requisite strength, flexibility, and resistance to fatigue,
conductors 20 formed of multi-strands of drawn-filled tubes, in accordance with the preferred embodiment, provide a low resistance alternative to other conventional materials. Specifically, a stranded wire, or even coiled wire, of approximately 60 cm and formed of MP35N or stainless steel or the like would have a measured resistance in excess of 30 ohms. In contrast, for the same length, a wire formed of multi-strands of drawn-filled tubes, as illustrated inFIG. 4 , could have a resistance less than 4 ohms. Accordingly, in a preferred embodiment, eachconductor 20, having a length equal to or less than 60 cm, has a resistance of less than 25 ohms. In a more preferred embodiment, eachconductor 20, having a length equal to or less than 60 cm, has a resistance equal to or less than 10 ohms. In a most preferred embodiment, eachconductor 20, having a length equal to or less than 60 cm, has a resistance of less than 4 ohms. - As an alternative embodiment,
body 22 can further encompass stylet tubing 24 (FIG. 3 ).Stylet tubing 24 extends from theproximal end 12 to a point within a distal portion oflead 10; however, in a preferred embodiment,stylet tubing 24 extends to capelectrode 34. In cooperative reference toFIG. 2 ,stylet tubing 24 operatively receivesstylet 100 for purposes of allowing better control overlead 10 during placement. - Lead Assembly
- While the following discussion provides but one example of a sequence of steps to form a lead similar to that illustrated in
FIGS. 2 and 3 . One having ordinary skill in this art shall appreciate that the following steps may be performed in a differing order or otherwise inconsequentially modified to still yield the present invention. Consequently, such minor variations are still regarded as being within the scope of the present invention and should be construed in such manner. - Furthermore, for purposes of illustration, the following example includes certain physical dimensions to illustrate the relationship between elements as well as effects of differing processes. Accordingly, the provided physical dimensions are used merely for example and shall not restrict the scope of the present invention.
- The following illustrative example concerns the construction of an eight electrode, epidural lead that accommodates a stylet. One skilled in the art shall appreciate, however, that a lead in accordance with the present invention may have more than or less than eight electrodes and/or have a larger or smaller diameter than the following example and remain within the scope of this disclosure.
- In reference to
FIG. 5 ,stylet tubing 24 is positioned overmandrel 150.Stylet tubing 24 has an outer diameter of approximately 0.02 inches. - Depending on the quantity of
conductors 20 required (e.g., for this illustration, eight) and the size (i.e., diameter) ofsuch conductors 20, arranging and securingconductors 20 can be problematic when they are being arranged and secured about an element having the dimensions ofstylet tubing 24. - While any number of techniques may be used to achieve such arrangement of
conductors 20 relative tostylet tubing 24,FIG. 11 illustrates an example of a fixture 200 that can assist in this task. Specifically, fixture 200 includes firstrotary clamp 202,iris 204,iris 206, secondrotary clamp 208, and clamp 210. Rotary clamps 202 and 208 each include a corresponding plurality of conductor clamps 203. While not required, it is preferred that the plurality of conductor clamps 203 of eachrotary claim arbitrary perimeter 205, whereasperimeter 205 should be equal to or greater than a fully-opened inner diameter of eitheriris - As illustrated,
mandrel 150, includingstylet tubing 24, passes throughirises rotary clamp 208 and is secured betweenclamps conductor 20 similarly passes throughirises respective clamps 203 of rotary clamps 202 and 208. -
Conductors 20 secured within fixture 200 are prepared for assembly in that a prescribed amount ofinsulative material 20 c is removed at or about the proximal and distal ends of eachconductor 20 to exposeconductive material conductive material conductor 20 is eventually joined to anelectrode 18 and a terminal 16. Accordingly, the exposedconductive material stylet tubing 24 to accommodate the serial arrangement ofterminals 16 andelectrodes 18. - The rotational nature of rotary clamps 202 and 208 provides unobstructed access to the in-
process lead 10. Specifically, upon securing asingle conductor 20 between opposing (or non-opposing) clamps 203, the rotary clamps 202 and 210 are simply rotated to allow access tounoccupied clamps 203. - When all of the
conductors 20 are strung betweenclaims irises stylet tubing 24. When conductor(s) 20 are resting against the outer diameter ofstylet tubing 24, conductor(s) 20 are secured in place. Conductor(s) 20 may be secured using adhesive and/or subjected to a force applied through use of a temporary or permanent restraint, for example, one or more crimped collars. - While the illustration of
FIG. 11 shows but one embodiment of fixture 200, one skilled in the art should appreciate that other techniques/structures may be employed to positionconductors 20 adjacent an exterior surface ofstylet tubing 24. Specifically, clamps 203 of eachrotary clamp conductors 20 to be moved from a first position to a second position adjacent the exterior surface ofstylet tubing 24. Alternatively,conductors 20 could initially be secured to one end ofstylet tubing 24 and only a single iris could be used to draw the unsecured portions ofconductors 20 towardstylet tubing 24. As yet another alternative, while the various alternatives offered provide some mechanism to control the rate of movement and relative positioning ofconductors 20, an operator could simply manipulate the conductor(s) 20 to manually position and secure them relative tostylet tubing 24. - Once all
conductors 20 are secured tostylet tubing 24,transitional element 26, electrode(s) 18, electrode spacer(s) 28,outer tubing 23, terminal spacer(s) 30, terminal(s) 16, andstylet guide 32 are positioned over, and concentrically arranged with,stylet tubing 24. The arrangement of these elements is in accordance with that illustrated inFIG. 5 . -
Transitional element 26 is illustrated inFIG. 6 . As will be discussed later,transitional element 26 provides a platform to receive cap electrode 34 (FIG. 10 ).Transitional element 26 further provides adurable guide 26 a to direct a distal end (not shown) ofstylet 100 to capelectrode 34 viapassage 26 b.Transitional element 26 is preferably formed of a conductive material, for example, the same material used to formelectrodes 18. -
Electrode spacer 28 is illustrated inFIG. 7 . Similarly,terminal spacer 30 is illustrated inFIG. 8 . Functionally,electrode spacer 28 andterminal spacer 30 accurately defines a space betweenadjacent electrodes 18 andterminals 16, respectively.Electrode spacer 28 andterminal spacer 30 are preferably formed of the same material asouter tubing 23. However,spacers outer tubing 23; provided however, any differing material used forelectrode spacer 28 and/orterminal spacer 30 must be compatible with and possess largely the same mechanical properties (e.g., non-reactive to the environment of the human body, flexible and durable) asouter tubing 23. At least for purposes of this example, spacers 28, and 30 are formed of a polyurethane material, for example, Bionate 75D (Polymer Tech. Group, City, State). As is noted inFIG. 5 ,spacers lead 10. -
Outer tubing 23separates electrodes 18 fromterminals 16. In a preferred embodiment,outer tubing 23 has a diameter substantially equal to a diameter oflead 10. Alternatively,outer tubing 23 may have a diameter less thanlead 10, or a diameter greater thanlead 10. In regard to the latter alternative,outer tubing 23 must have a wall thickness greater than a differential between a radius oflead 10 and a radius (to the outer diameter) ofouter tubing 23. For this particular example,outer tubing 23 has a nominal outer diameter of approximate 0.055 inches. -
Stylet guide 32 is illustrated inFIG. 9 .Stylet guide 32 provides an inlet tostylet tubing 24.Stylet guide 32 is preferably formed of conductive material, for example, the same material used to formelectrodes 18.Stylet guide 32, as well asterminals 16,electrodes 18, andtransitional element 26, preferably each have an outer diameter equal to or greater than a nominal diameter oflead 10. In a more preferred embodiment, these elements each have an outer diameter greater than a nominal diameter oflead 10. - Following the assembly of each of the elements described above,
terminals 16 andelectrodes 18 are joined to theirrespective conductors 20. Generally, each terminal 16 (and each electrode 18) is positioned relative to exposedconductive material conductor 20 and is joined in a manner that facilitates a transfer of electrical energy, for example, resistance weld or laser weld. Once allterminals 16 andelectrodes 18 are secured,stylet guide 32 is secured to aproximal-most terminal 16, andtransitional element 26 is secured to adistal-most electrode 18. Providedtransitional element 26 andstylet guide 32 are formed a conductive material, these elements may be secured using a process consistent with that used to jointerminals 16 andelectrodes 18 withconductors 20. Otherwise,transitional element 26 and stylet guide 32 can be joined using an adhesive, cement or the like. - The completed assembly (
FIG. 5 ) is then over-molded, using well known injection molding techniques, using a material having mechanical properties consistent with a material(s) used to formouter tubing 23,electrode spacer 28, andterminal spacer 30. In a preferred embodiment, the over-molding material and the material ofouter tubing 23,electrode spacer 28, and terminal 28 are the same. - This process has the beneficial effect of unitizing the element assembly to form
lead 10. Moreover,electrode spacers 28 andterminal spacers 30 are placed in a state of flow, which, at least in part, results in a filling of regions betweenterminals 16/electrodes 18 andstylet guide 24. Consequently,terminals 16 andelectrodes 18 are partially surrounded (i.e., along an interior surface) and supported by a fused matrix of; material. Importantly, aselectrode spacers 28 andterminal spacers 30 are formed of a material mechanically equivalent to that ofbody 22/outer tubing 23, the stimulation/sensing portion and terminal portion oflead 10 are stabilized and strengthened while also retaining their flexible properties. - The over-molded assembly (not shown) is then subjected to a grinding process to remove all excess material. In a preferred process, the over-molded assembly is subject to centerless grinding, wherein excessive material, including over-molded material, electrode material, terminal material, and the like, is removed. Pursuant to the described over-molding and grinding of the entire lead assembly, an isodiametric lead is obtained, which is further free of any gaps or voids between insulative material and conductive material that may otherwise exist in conventional devices.
- Following the grinding process,
cap electrode 34 is affixed totransitional element 26 using conventional means, for example, resistance welding, laser welding, or the like. - While addressed in part above, as the invention has been described herein relative to a number of particularized embodiments, it is understood that modifications of, and alternatives to, these embodiments, such modifications and alternatives realizing the advantages and benefits of this invention, will be apparent to those of ordinary skill in the art having reference to this specification and its drawings. It is contemplated that such modifications and alternatives are within the scope of this invention as subsequently claimed herein, and it is intended that the scope of this invention claimed herein be limited only by the broadest interpretation of the appended claims to which the inventors are legally entitled.
Claims (21)
1.-14. (canceled)
15. An implantable lead comprising:
a lead body having a distal end and a proximal end having a terminal;
a first region extending distally from the distal end of the lead body, wherein the first region includes a plurality of electrodes, and adjacent electrodes are separated by a first insulative material having prescribed mechanical properties;
at least one conductor electrically coupling the terminal with at least one corresponding electrode of the plurality of electrodes, wherein the at least one conductor extends along the lead body and the first region, and
wherein in addition to the at least one conductor, a portion of the first region is substantially filled with a second insulative material having mechanical properties consistent with the first insulative material.
16. An implantable lead in accordance with claim 15 wherein the first insulative material and the second insulative material are the same.
17. An implantable lead in accordance with claim 15 wherein the lead body is formed of a material having properties consistent with the first insulative material.
18. An implantable lead in accordance with claim 15 wherein the at least one conductor is formed of stranded wire and has a resistance equal to or less than 25 ohms for a conductor length equal to or less than 60 cm.
19. An implantable lead in accordance with claim 15 wherein an outer diameter of the lead body is approximately 0.05 inches.
20. An implantable lead in accordance with claim 15 further comprising a stylet guide, positioned within the lead body and the first region, and the second material substantially surrounds the stylet guide.
21. An implantable lead in accordance with claim 15 wherein the implantable lead is substantially isodiametric.
22. An implantable lead in accordance with claim 15 wherein the second insulative material is a fused matrix.
23. An implantable lead in accordance with claim 15 wherein at least one interior passage is within a second region extending proximally from the proximal end of the lead body, and in addition to the at least one conductor, the interior passage of the second region is substantially filled with a third insulative material having mechanical properties consistent with the first insulative material.
24. An implantable lead in accordance with claim 23 wherein the first insulative material, the second insulative material, and the third insulative material are the same.
25. An implantable lead in accordance with claim 23 , wherein the third insulative material is a fused matrix.
26. An implantable lead in accordance with claim 15 wherein the at least one conductor has a resistance less than 4 ohms for a conductor length equal to or less than 60 cm.
27. An implantable lead in accordance with claim 26 wherein an outer diameter of the lead body is approximately 0.05 inches.
28. An implantable lead in accordance with claim 15 wherein the at least one conductor has a resistance less than 4 ohms.
29. An implantable lead in accordance with claim 15 wherein the corresponding electrode is joined to the at least one conductor by a laser weld.
30. An implantable lead in accordance with claim 15 wherein the plurality of electrodes equals eight.
31. An implantable lead comprising:
a lead body having a distal end and a proximal end having a terminal;
a first region extending distally from the distal end of the lead body, wherein the first region includes a plurality of electrodes, and adjacent electrodes are separated by a first insulative material having prescribed mechanical properties;
at least one conductor electrically coupling the terminal with at least one corresponding electrode of the plurality of electrodes, wherein the at least one conductor extends through at least a portion of each of the lead body and the first region; and
wherein at least the first region has a substantially solid cross-section, and excepting the at least one conductor passing therethrough and the plurality of electrodes thereof, material(s) forming the first region has mechanical properties consistent with the first insulative material.
32. An implantable lead in accordance with claim 31 wherein the material(s) forming the first region, which supports the plurality of electrodes and carries the at least one conductor, is a fused matrix.
33. An implantable lead comprising:
a lead body having a distal end and a proximal end having a terminal;
a stimulation portion extending distally from the distal end of the lead body, wherein the stimulation portion includes a plurality of electrodes, and adjacent electrodes are separated by an insulative material having prescribed mechanical properties;
at least one conductor electrically coupling the terminal with at least one corresponding electrode of the plurality of electrodes, wherein the at least one conductor extends through at least a portion of each of the lead body and the stimulation portion; and
wherein at least the stimulation portion is formed from a substantially solid, fused matrix of materials having consistent mechanical characteristics, and the fused matrix of material(s) supports the plurality of electrodes and the at least one conductor extends at least partially therethrough.
34. An implantable lead comprising:
a lead body having a distal end and a proximal end having a terminal;
a first region extending distally from the distal end of the lead body, wherein the first region includes a plurality of electrodes, and adjacent electrodes are separated by a first insulative material, the first insulative material having prescribed mechanical properties;
at least one conductor electrically coupling the terminal with at least one corresponding electrode of the plurality of electrodes, wherein the at least one conductor extends along within the lead body and the first region, and
wherein in addition to the at least one conductor, the a portion of the first region is substantially filled with a second insulative material having mechanical properties consistent with material of the first insulative material.
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US13/617,187 Expired - Fee Related US8671566B2 (en) | 1999-04-26 | 2012-09-14 | Method of forming a lead |
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US13/617,187 Expired - Fee Related US8671566B2 (en) | 1999-04-26 | 2012-09-14 | Method of forming a lead |
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US7206642B2 (en) * | 2002-04-22 | 2007-04-17 | Medtronic, Inc. | Implantable lead with improved stylet lumen |
US7184840B2 (en) * | 2002-04-22 | 2007-02-27 | Medtronic, Inc. | Implantable lead with isolated contact coupling |
WO2003101532A2 (en) * | 2002-06-04 | 2003-12-11 | Cyberkinetics, Inc. | Optically-connected implants and related systems and methods of use |
US6792318B2 (en) | 2002-06-13 | 2004-09-14 | Pacesetter, Inc. | Technique for fixating a lead |
US7203548B2 (en) | 2002-06-20 | 2007-04-10 | Advanced Bionics Corporation | Cavernous nerve stimulation via unidirectional propagation of action potentials |
US7292890B2 (en) | 2002-06-20 | 2007-11-06 | Advanced Bionics Corporation | Vagus nerve stimulation via unidirectional propagation of action potentials |
US7860570B2 (en) | 2002-06-20 | 2010-12-28 | Boston Scientific Neuromodulation Corporation | Implantable microstimulators and methods for unidirectional propagation of action potentials |
US20040015205A1 (en) * | 2002-06-20 | 2004-01-22 | Whitehurst Todd K. | Implantable microstimulators with programmable multielectrode configuration and uses thereof |
US7212851B2 (en) | 2002-10-24 | 2007-05-01 | Brown University Research Foundation | Microstructured arrays for cortex interaction and related methods of manufacture and use |
US20040215305A1 (en) * | 2003-04-25 | 2004-10-28 | Sage Shahn S. | Implantable lead with intermediate insertion port for receiving a stiffening member |
US20040249302A1 (en) * | 2003-06-09 | 2004-12-09 | Cyberkinetics, Inc. | Methods and systems for processing of brain signals |
US7502649B2 (en) * | 2003-06-20 | 2009-03-10 | Metacure Ltd. | Gastrointestinal methods and apparatus for use in treating disorders |
US20070060971A1 (en) * | 2003-07-21 | 2007-03-15 | Ofer Glasberg | Hepatic device for treatment or glucose detection |
US8792985B2 (en) | 2003-07-21 | 2014-07-29 | Metacure Limited | Gastrointestinal methods and apparatus for use in treating disorders and controlling blood sugar |
US20050027338A1 (en) * | 2003-07-29 | 2005-02-03 | Advanced Neuromodulation Systems, Inc. | Stretchable lead body, method of manufacture, and system |
US20050027341A1 (en) * | 2003-07-29 | 2005-02-03 | Micronet Medical, Inc. | System and method for providing a medical lead body having conductors that are wound in opposite directions |
US20050027340A1 (en) * | 2003-07-29 | 2005-02-03 | Micronet Medical, Inc. | System and method for providing a medical lead body having dual conductor layers |
US20050027339A1 (en) * | 2003-07-29 | 2005-02-03 | Micronet Medical, Inc. | System and method for providing a medical lead body |
US20050038489A1 (en) * | 2003-08-14 | 2005-02-17 | Grill Warren M. | Electrode array for use in medical stimulation and methods thereof |
US8340779B2 (en) | 2003-08-29 | 2012-12-25 | Medtronic, Inc. | Percutaneous flat lead introducer |
US20050049663A1 (en) * | 2003-08-29 | 2005-03-03 | Harris Charmaine K. | Percutaneous flat lead introducer |
US20050065586A1 (en) * | 2003-09-22 | 2005-03-24 | Michael Johnson | Medical device having arbitrarily-shaped electrodes |
US20050080325A1 (en) * | 2003-10-14 | 2005-04-14 | Advanced Neuromodulation Systems, Inc. | Low profile connector and system for implantable medical device |
US20050143589A1 (en) * | 2003-11-09 | 2005-06-30 | Donoghue John P. | Calibration systems and methods for neural interface devices |
US7702396B2 (en) | 2003-11-21 | 2010-04-20 | Advanced Bionics, Llc | Optimizing pitch allocation in a cochlear implant |
US20050113744A1 (en) * | 2003-11-21 | 2005-05-26 | Cyberkinetics, Inc. | Agent delivery systems and related methods under control of biological electrical signals |
US7751877B2 (en) * | 2003-11-25 | 2010-07-06 | Braingate Co., Llc | Neural interface system with embedded id |
US20050159799A1 (en) * | 2003-11-25 | 2005-07-21 | Advanced Neuromodulation Systems, Inc. | Percutaneous-insertion needle and method of implanting a lead |
US8060207B2 (en) | 2003-12-22 | 2011-11-15 | Boston Scientific Scimed, Inc. | Method of intravascularly delivering stimulation leads into direct contact with tissue |
US20050137646A1 (en) * | 2003-12-22 | 2005-06-23 | Scimed Life Systems, Inc. | Method of intravascularly delivering stimulation leads into brain |
US7647097B2 (en) * | 2003-12-29 | 2010-01-12 | Braingate Co., Llc | Transcutaneous implant |
US7295875B2 (en) * | 2004-02-20 | 2007-11-13 | Boston Scientific Scimed, Inc. | Method of stimulating/sensing brain with combination of intravascularly and non-vascularly delivered leads |
US20050203600A1 (en) * | 2004-03-12 | 2005-09-15 | Scimed Life Systems, Inc. | Collapsible/expandable tubular electrode leads |
US7177702B2 (en) * | 2004-03-12 | 2007-02-13 | Scimed Life Systems, Inc. | Collapsible/expandable electrode leads |
US7590454B2 (en) * | 2004-03-12 | 2009-09-15 | Boston Scientific Neuromodulation Corporation | Modular stimulation lead network |
US20050203366A1 (en) * | 2004-03-12 | 2005-09-15 | Donoghue John P. | Neurological event monitoring and therapy systems and related methods |
US20050228469A1 (en) * | 2004-04-12 | 2005-10-13 | Cardiac Pacemakers, Inc. | Electrode and conductor interconnect and method therefor |
US20070276458A1 (en) * | 2004-04-23 | 2007-11-29 | Boser Gregory A | Novel medical device conductor junctions |
US7715926B2 (en) * | 2004-04-23 | 2010-05-11 | Medtronic, Inc. | Medical device conductor junctions |
US7389148B1 (en) | 2004-05-05 | 2008-06-17 | Pacesetter, Inc. | Electrode design for defibrillation and/or sensing capabilities |
US7231260B2 (en) | 2004-05-06 | 2007-06-12 | Boston Scientific Scimed, Inc. | Intravascular self-anchoring electrode body with arcuate springs, spring loops, or arms |
US7489971B1 (en) | 2004-06-05 | 2009-02-10 | Advanced Neuromodulation Systems, Inc. | Notched electrode for electrostimulation lead |
US7286879B2 (en) | 2004-07-16 | 2007-10-23 | Boston Scientific Scimed, Inc. | Method of stimulating fastigium nucleus to treat neurological disorders |
US20060049957A1 (en) * | 2004-08-13 | 2006-03-09 | Surgenor Timothy R | Biological interface systems with controlled device selector and related methods |
US8612016B2 (en) * | 2004-08-18 | 2013-12-17 | Metacure Limited | Monitoring, analysis, and regulation of eating habits |
US8214047B2 (en) * | 2004-09-27 | 2012-07-03 | Advanced Neuromodulation Systems, Inc. | Method of using spinal cord stimulation to treat gastrointestinal and/or eating disorders or conditions |
WO2006041738A2 (en) | 2004-10-04 | 2006-04-20 | Cyberkinetics Neurotechnology Systems, Inc. | Biological interface system |
US20060100672A1 (en) * | 2004-11-05 | 2006-05-11 | Litvak Leonid M | Method and system of matching information from cochlear implants in two ears |
US7522961B2 (en) * | 2004-11-17 | 2009-04-21 | Advanced Bionics, Llc | Inner hair cell stimulation model for the use by an intra-cochlear implant |
US7242985B1 (en) * | 2004-12-03 | 2007-07-10 | Advanced Bionics Corporation | Outer hair cell stimulation model for the use by an intra—cochlear implant |
US7599500B1 (en) | 2004-12-09 | 2009-10-06 | Advanced Bionics, Llc | Processing signals representative of sound based on the identity of an input element |
US7937160B2 (en) * | 2004-12-10 | 2011-05-03 | Boston Scientific Neuromodulation Corporation | Methods for delivering cortical electrode leads into patient's head |
US7450994B1 (en) * | 2004-12-16 | 2008-11-11 | Advanced Bionics, Llc | Estimating flap thickness for cochlear implants |
US9517488B2 (en) | 2004-12-30 | 2016-12-13 | Plas-Pak Industries, Inc. | Component delivery system utilizing film bags |
US20100108709A1 (en) * | 2004-12-30 | 2010-05-06 | Plas-Pak Industries | Cartridge delivery system utilizing film bags |
WO2006074029A2 (en) * | 2005-01-06 | 2006-07-13 | Cyberkinetics Neurotechnology Systems, Inc. | Neurally controlled and multi-device patient ambulation systems and related methods |
US8095209B2 (en) * | 2005-01-06 | 2012-01-10 | Braingate Co., Llc | Biological interface system with gated control signal |
US20070032738A1 (en) * | 2005-01-06 | 2007-02-08 | Flaherty J C | Adaptive patient training routine for biological interface system |
US20060189901A1 (en) * | 2005-01-10 | 2006-08-24 | Flaherty J C | Biological interface system with surrogate controlled device |
US20060189899A1 (en) * | 2005-01-10 | 2006-08-24 | Flaherty J Christopher | Joint movement apparatus |
US8019439B2 (en) * | 2005-01-11 | 2011-09-13 | Boston Scientific Neuromodulation Corporation | Lead assembly and method of making same |
US7891085B1 (en) * | 2005-01-11 | 2011-02-22 | Boston Scientific Neuromodulation Corporation | Electrode array assembly and method of making same |
US8204570B2 (en) * | 2005-01-12 | 2012-06-19 | Maquet Critical Care Ab | Electrode for physiological signal measurements and method for making same |
US8060194B2 (en) * | 2005-01-18 | 2011-11-15 | Braingate Co., Llc | Biological interface system with automated configuration |
US7840279B2 (en) | 2005-02-11 | 2010-11-23 | Boston Scientific Neuromodulation Corporation | Implantable microstimulator having a separate battery unit and methods of use thereof |
US9821158B2 (en) | 2005-02-17 | 2017-11-21 | Metacure Limited | Non-immediate effects of therapy |
US7627383B2 (en) | 2005-03-15 | 2009-12-01 | Boston Scientific Neuromodulation Corporation | Implantable stimulator |
US20110077579A1 (en) * | 2005-03-24 | 2011-03-31 | Harrison William V | Cochlear implant with localized fluid transport |
WO2007080595A2 (en) * | 2006-01-12 | 2007-07-19 | Metacure N.V. | Electrode assemblies, tools, and methods for gastric wall implantation |
US7801602B2 (en) * | 2005-04-08 | 2010-09-21 | Boston Scientific Neuromodulation Corporation | Controlling stimulation parameters of implanted tissue stimulators |
US20110040350A1 (en) * | 2005-05-05 | 2011-02-17 | Griffith Glen A | FSK telemetry for cochlear implant |
US7801600B1 (en) * | 2005-05-26 | 2010-09-21 | Boston Scientific Neuromodulation Corporation | Controlling charge flow in the electrical stimulation of tissue |
EP1890763A4 (en) * | 2005-06-02 | 2017-05-03 | Metacure Limited | Gi lead implantation |
US7792591B2 (en) * | 2005-06-09 | 2010-09-07 | Medtronic, Inc. | Introducer for therapy delivery elements |
US20090222064A1 (en) * | 2005-07-08 | 2009-09-03 | Advanced Bionics, Llc | Autonomous Autoprogram Cochlear Implant |
US8175717B2 (en) * | 2005-09-06 | 2012-05-08 | Boston Scientific Neuromodulation Corporation | Ultracapacitor powered implantable pulse generator with dedicated power supply |
US8442841B2 (en) | 2005-10-20 | 2013-05-14 | Matacure N.V. | Patient selection method for assisting weight loss |
US20100331913A1 (en) * | 2005-10-28 | 2010-12-30 | Mann Alfred E | Hybrid multi-function electrode array |
US7567840B2 (en) * | 2005-10-28 | 2009-07-28 | Cyberonics, Inc. | Lead condition assessment for an implantable medical device |
US8027733B1 (en) | 2005-10-28 | 2011-09-27 | Advanced Bionics, Llc | Optimizing pitch allocation in a cochlear stimulation system |
US20070106143A1 (en) * | 2005-11-08 | 2007-05-10 | Flaherty J C | Electrode arrays and related methods |
US7729758B2 (en) * | 2005-11-30 | 2010-06-01 | Boston Scientific Neuromodulation Corporation | Magnetically coupled microstimulators |
US8295932B2 (en) * | 2005-12-05 | 2012-10-23 | Metacure Limited | Ingestible capsule for appetite regulation |
US20100023021A1 (en) * | 2005-12-27 | 2010-01-28 | Flaherty J Christopher | Biological Interface and Insertion |
US20070156126A1 (en) * | 2005-12-29 | 2007-07-05 | Flaherty J C | Medical device insertion system and related methods |
US7729781B2 (en) * | 2006-03-16 | 2010-06-01 | Greatbatch Ltd. | High efficiency neurostimulation lead |
US7729775B1 (en) | 2006-03-21 | 2010-06-01 | Advanced Bionics, Llc | Spectral contrast enhancement in a cochlear implant speech processor |
US8180462B2 (en) | 2006-04-18 | 2012-05-15 | Cyberonics, Inc. | Heat dissipation for a lead assembly |
US8818517B2 (en) * | 2006-05-05 | 2014-08-26 | Advanced Bionics Ag | Information processing and storage in a cochlear stimulation system |
US8478420B2 (en) * | 2006-07-12 | 2013-07-02 | Cyberonics, Inc. | Implantable medical device charge balance assessment |
US20080027524A1 (en) * | 2006-07-26 | 2008-01-31 | Maschino Steven E | Multi-electrode assembly for an implantable medical device |
US8321025B2 (en) | 2006-07-31 | 2012-11-27 | Cranial Medical Systems, Inc. | Lead and methods for brain monitoring and modulation |
US7995771B1 (en) | 2006-09-25 | 2011-08-09 | Advanced Bionics, Llc | Beamforming microphone system |
US7864968B2 (en) * | 2006-09-25 | 2011-01-04 | Advanced Bionics, Llc | Auditory front end customization |
US7857819B2 (en) * | 2006-11-30 | 2010-12-28 | Boston Scientific Neuromodulation Corporation | Implant tool for use with a microstimulator |
US20080147158A1 (en) * | 2006-12-18 | 2008-06-19 | Quan Emerteq Corp. | Implantable Medical Lead Having Coil Electrode |
US8160719B2 (en) * | 2006-12-19 | 2012-04-17 | Greatbatch Ltd. | Braided electrical lead |
US7974707B2 (en) * | 2007-01-26 | 2011-07-05 | Cyberonics, Inc. | Electrode assembly with fibers for a medical device |
US7899548B2 (en) * | 2007-07-05 | 2011-03-01 | Boston Scientific Neuromodulation Corporation | Lead with contacts formed by coiled conductor and methods of manufacture and use |
US7877136B1 (en) | 2007-09-28 | 2011-01-25 | Boston Scientific Neuromodulation Corporation | Enhancement of neural signal transmission through damaged neural tissue via hyperpolarizing electrical stimulation current |
US8942798B2 (en) | 2007-10-26 | 2015-01-27 | Cyberonics, Inc. | Alternative operation mode for an implantable medical device based upon lead condition |
US8868203B2 (en) | 2007-10-26 | 2014-10-21 | Cyberonics, Inc. | Dynamic lead condition detection for an implantable medical device |
US8364284B2 (en) | 2008-09-15 | 2013-01-29 | Boston Scientific Neuromodulation Corporation | Implantable electric stimulation system and methods of making and using |
DE102008008927A1 (en) * | 2008-02-13 | 2009-08-20 | Biotronik Crm Patent Ag | Electrode lead and fitting for electromedical implants |
US8412351B2 (en) * | 2008-03-21 | 2013-04-02 | Medtronic, Inc. | System and method for shunting induced currents in an electrical lead |
US8600518B2 (en) * | 2008-04-30 | 2013-12-03 | Boston Scientific Neuromodulation Corporation | Electrodes for stimulation leads and methods of manufacture and use |
KR20110058771A (en) * | 2008-06-20 | 2011-06-01 | 코치리어 리미티드 | Strain relief in an implantable electrode assembly |
US9351655B2 (en) | 2008-09-02 | 2016-05-31 | Boston Scientific Neuromodulation Corporation | Systems, devices, and methods for electrically coupling terminals to electrodes of electrical stimulation systems |
US7941227B2 (en) * | 2008-09-03 | 2011-05-10 | Boston Scientific Neuromodulation Corporation | Implantable electric stimulation system and methods of making and using |
US9403020B2 (en) | 2008-11-04 | 2016-08-02 | Nevro Corporation | Modeling positions of implanted devices in a patient |
US8712542B2 (en) * | 2008-11-04 | 2014-04-29 | Boston Scientific Neuromodulation Corporation | Deposited conductive layers for leads of implantable electric stimulation systems and methods of making and using |
US20100210146A1 (en) * | 2009-02-18 | 2010-08-19 | Pacesetter, Inc. | Lead connector end and method of manufacture |
US8478424B2 (en) * | 2009-02-23 | 2013-07-02 | Medtronic, Inc. | Medical lead having coaxial connector |
US8061026B2 (en) * | 2009-02-23 | 2011-11-22 | Medtronic, Inc. | Method for making smooth transitions between differing lead segments |
US8473061B2 (en) | 2009-04-16 | 2013-06-25 | Boston Scientific Neuromodulation Corporation | Deep brain stimulation current steering with split electrodes |
US8046909B2 (en) * | 2009-04-24 | 2011-11-01 | Advanced Neuromodulation Systems, Inc. | Method of fabricating stimulation lead |
US8322026B2 (en) | 2009-06-29 | 2012-12-04 | Boston Scientific Neuromodulation Corporation | Method for forming a lead |
US8406896B2 (en) * | 2009-06-29 | 2013-03-26 | Boston Scientific Neuromodulation Corporation | Multi-element contact assemblies for electrical stimulation systems and systems and methods of making and using |
US8887387B2 (en) | 2009-07-07 | 2014-11-18 | Boston Scientific Neuromodulation Corporation | Methods of manufacture of leads with a radially segmented electrode array |
US8875391B2 (en) | 2009-07-07 | 2014-11-04 | Boston Scientific Neuromodulation Corporation | Methods for making leads with radially-aligned segmented electrodes for electrical stimulation systems |
US8249721B2 (en) | 2009-07-13 | 2012-08-21 | Boston Scientific Neuromodulation Corporation | Method for fabricating a neurostimulation lead contact array |
US8380325B2 (en) * | 2009-08-05 | 2013-02-19 | Boston Scientific Neuromodulation Corporation | Systems and methods for coupling coiled conductors to conductive contacts of an electrical stimulation system |
US8406897B2 (en) | 2009-08-19 | 2013-03-26 | Boston Scientific Neuromodulation Corporation | Systems and methods for disposing one or more layers of material between lead conductor segments of electrical stimulation systems |
WO2011028809A1 (en) | 2009-09-01 | 2011-03-10 | Advanced Neuromodulation Systems, Inc. | Medical leads with segmented electrodes and methods of fabrication thereof |
US8171621B2 (en) * | 2009-09-30 | 2012-05-08 | Advanced Neuromodulation Systems, Inc. | Methods of fabrication of a simulation lead |
US11045221B2 (en) * | 2009-10-30 | 2021-06-29 | Medtronic, Inc. | Steerable percutaneous paddle stimulation lead |
US8874232B2 (en) | 2009-11-30 | 2014-10-28 | Boston Scientific Neuromodulation Corporation | Electrode array having concentric split ring electrodes and methods of making the same |
US8934975B2 (en) | 2010-02-01 | 2015-01-13 | Metacure Limited | Gastrointestinal electrical therapy |
EP2552540B1 (en) | 2010-03-31 | 2016-05-11 | Advanced Neuromodulation Systems, Inc. | Method of fabricating implantable pulse generator using wire connections to feedthrough structures and implantable pulse generators |
US8478428B2 (en) | 2010-04-23 | 2013-07-02 | Cyberonics, Inc. | Helical electrode for nerve stimulation |
US8521305B2 (en) | 2010-05-11 | 2013-08-27 | St. Jude Medical, Inc. | Percutaneous lead with distal fixation |
JP5793190B2 (en) | 2010-06-18 | 2015-10-14 | ボストン サイエンティフィック ニューロモデュレイション コーポレイション | Method for manufacturing a brain stimulator |
US8583237B2 (en) | 2010-09-13 | 2013-11-12 | Cranial Medical Systems, Inc. | Devices and methods for tissue modulation and monitoring |
ES2506441T3 (en) | 2010-09-21 | 2014-10-13 | Boston Scientific Neuromodulation Corporation | Systems and methods for manufacturing and using radially aligned segmented electrodes for electrical stimulation system cables |
US8805519B2 (en) | 2010-09-30 | 2014-08-12 | Nevro Corporation | Systems and methods for detecting intrathecal penetration |
EP2455131B1 (en) * | 2010-11-19 | 2013-01-23 | Sorin CRM SAS | Probe for stimulating a left cavity of the heart which can be implanted in the coronary network |
JP5889917B2 (en) * | 2010-12-23 | 2016-03-22 | ボストン サイエンティフィック ニューロモデュレイション コーポレイション | Method of manufacturing a lead having segmented electrodes for an electrical stimulation system |
US8700179B2 (en) | 2011-02-02 | 2014-04-15 | Boston Scientific Neuromodulation Corporation | Leads with spiral of helical segmented electrode arrays and methods of making and using the leads |
US20120203316A1 (en) | 2011-02-08 | 2012-08-09 | Boston Scientific Neuromodulation Corporation | Leads with segmented electrodes for electrical stimulation of planar regions and methods of making and using |
WO2012109331A1 (en) | 2011-02-08 | 2012-08-16 | Boston Scientific Neuromodulation Corporation | Leads with spirally arranged segmented electrodes and methods of making and using the leads |
EP2664354B1 (en) * | 2012-05-16 | 2015-09-16 | Sorin CRM SAS | Medical lead with a ring electrode for implantation in a cardiac or cerebral blood vessel and a method for its manufacture |
US8897891B2 (en) | 2012-08-03 | 2014-11-25 | Boston Scientific Neuromodulation Corporation | Leads with electrode carrier for segmented electrodes and methods of making and using |
WO2014031356A1 (en) * | 2012-08-24 | 2014-02-27 | Boston Scientific Neuromodulation Corporation | Systems and methods for improving rf compatibility of electrical stimulation leads |
EP2719422B1 (en) * | 2012-10-12 | 2015-02-18 | Sorin CRM SAS | Implantable multipolar detection/stimulation microprobe |
WO2014089213A1 (en) * | 2012-12-06 | 2014-06-12 | Boston Scientific Neuromodulation Corporation | Systems and methods of forming contact assemblies for leads of electrical stimulation systems |
US9878170B2 (en) | 2013-03-15 | 2018-01-30 | Globus Medical, Inc. | Spinal cord stimulator system |
US9872997B2 (en) | 2013-03-15 | 2018-01-23 | Globus Medical, Inc. | Spinal cord stimulator system |
US9887574B2 (en) | 2013-03-15 | 2018-02-06 | Globus Medical, Inc. | Spinal cord stimulator system |
US9440076B2 (en) | 2013-03-15 | 2016-09-13 | Globus Medical, Inc. | Spinal cord stimulator system |
US9248272B2 (en) | 2013-05-31 | 2016-02-02 | Boston Scientific Neuromodulation Corporation | Segmented electrode leads formed from pre-electrodes with depressions or apertures and methods of making and using |
US9498620B2 (en) | 2013-05-31 | 2016-11-22 | Boston Scientific Neuromodulation Corporation | Leads containing segmented electrodes with non-perpendicular legs and methods of making and using |
CA2911235C (en) | 2013-05-31 | 2017-11-07 | Boston Scientific Neuromodulation Corporation | Leads with segmented electrodes and methods of making the leads |
EP3003466B1 (en) | 2013-05-31 | 2019-07-17 | Boston Scientific Neuromodulation Corporation | Segmented electrode leads formed from pre-electrodes with alignment features and methods of making the leads |
AU2014287516A1 (en) | 2013-07-12 | 2016-01-21 | Boston Scientific Neuromodulation Corporation | Leads with segmented electrodes and methods of making and using the leads |
CN105392523A (en) | 2013-07-22 | 2016-03-09 | 波士顿科学神经调制公司 | Methods of manufacturing molded segmented electrode leads |
US9775988B2 (en) | 2013-12-02 | 2017-10-03 | Boston Scientific Neuromodulation Corporation | Electrical stimulation leads with helically arranged electrodes and methods of making and using |
US9757555B2 (en) | 2014-04-24 | 2017-09-12 | Medtronic, Inc. | Pre-molded sub-assemblies for implantable medical leads |
JP2017517374A (en) | 2014-06-13 | 2017-06-29 | ボストン サイエンティフィック ニューロモデュレイション コーポレイション | Lead having an electrode carrier for a segment electrode and method for manufacturing and using the same |
US9770598B2 (en) | 2014-08-29 | 2017-09-26 | Boston Scientific Neuromodulation Corporation | Systems and methods for making and using improved connector contacts for electrical stimulation systems |
US9561362B2 (en) | 2014-11-10 | 2017-02-07 | Boston Scientific Neuromodulation Corporation | Systems and methods for making and using improved contact arrays for electrical stimulation systems |
US9604068B2 (en) | 2014-11-10 | 2017-03-28 | Boston Scientific Neuromodulation Corporation | Systems and methods for making and using improved connector contacts for electrical stimulation systems |
EP3229891B1 (en) | 2015-02-06 | 2019-08-14 | Boston Scientific Neuromodulation Corporation | Systems with improved contact arrays for electrical stimulation systems |
EP3058983B1 (en) | 2015-02-17 | 2021-10-13 | Sorin CRM SAS | Detection/stimulation microprobe, in particular for multipoint neuromodulation of the central nervous system |
WO2016164361A1 (en) | 2015-04-10 | 2016-10-13 | Boston Scientific Neuromodulation Corporation | Systems and methods for making and using improved contact arrays for electrical stimulation systems |
US9364659B1 (en) | 2015-04-27 | 2016-06-14 | Dantam K. Rao | Smart lead for deep brain stimulation |
US9656093B2 (en) | 2015-07-16 | 2017-05-23 | Boston Scientific Neuromodulation Corporation | Systems and methods for making and using connector contact arrays for electrical stimulation systems |
US9956394B2 (en) | 2015-09-10 | 2018-05-01 | Boston Scientific Neuromodulation Corporation | Connectors for electrical stimulation systems and methods of making and using |
US10413737B2 (en) | 2015-09-25 | 2019-09-17 | Boston Scientific Neuromodulation Corporation | Systems and methods for providing therapy using electrical stimulation to disrupt neuronal activity |
US10342983B2 (en) | 2016-01-14 | 2019-07-09 | Boston Scientific Neuromodulation Corporation | Systems and methods for making and using connector contact arrays for electrical stimulation systems |
US10201713B2 (en) | 2016-06-20 | 2019-02-12 | Boston Scientific Neuromodulation Corporation | Threaded connector assembly and methods of making and using the same |
EP3263483A1 (en) | 2016-07-01 | 2018-01-03 | Sulzer Mixpac AG | Cartridge, core, mold and method of manufacturing a cartridge |
EP3263482B1 (en) | 2016-07-01 | 2018-09-19 | Sulzer Mixpac AG | Cartridge, core, mold and method of manufacturing a cartridge |
US10307602B2 (en) | 2016-07-08 | 2019-06-04 | Boston Scientific Neuromodulation Corporation | Threaded connector assembly and methods of making and using the same |
US10543374B2 (en) | 2016-09-30 | 2020-01-28 | Boston Scientific Neuromodulation Corporation | Connector assemblies with bending limiters for electrical stimulation systems and methods of making and using same |
US10576269B2 (en) | 2017-01-03 | 2020-03-03 | Boston Scientific Neuromodulation Corporation | Force-decoupled and strain relieving lead and methods of making and using |
US10905871B2 (en) | 2017-01-27 | 2021-02-02 | Boston Scientific Neuromodulation Corporation | Lead assemblies with arrangements to confirm alignment between terminals and contacts |
WO2018160495A1 (en) | 2017-02-28 | 2018-09-07 | Boston Scientific Neuromodulation Corporation | Toolless connector for latching stimulation leads and methods of making and using |
WO2018165391A1 (en) | 2017-03-09 | 2018-09-13 | Nevro Corp. | Paddle leads and delivery tools, and associated systems and methods |
US10603499B2 (en) | 2017-04-07 | 2020-03-31 | Boston Scientific Neuromodulation Corporation | Tapered implantable lead and connector interface and methods of making and using |
US10918873B2 (en) | 2017-07-25 | 2021-02-16 | Boston Scientific Neuromodulation Corporation | Systems and methods for making and using an enhanced connector of an electrical stimulation system |
WO2019055846A1 (en) | 2017-09-15 | 2019-03-21 | Boston Scientific Neuromodulation Corporation | Biased lead connector for operating room cable assembly and methods of making and using |
WO2019055837A1 (en) | 2017-09-15 | 2019-03-21 | Boston Scientific Neuromodulation Corporation | Actuatable lead connector for an operating room cable assembly and methods of making and using |
US11139603B2 (en) | 2017-10-03 | 2021-10-05 | Boston Scientific Neuromodulation Corporation | Connectors with spring contacts for electrical stimulation systems and methods of making and using same |
US11103712B2 (en) | 2018-01-16 | 2021-08-31 | Boston Scientific Neuromodulation Corporation | Connector assemblies with novel spacers for electrical stimulation systems and methods of making and using same |
EP3758793A4 (en) | 2018-03-29 | 2021-12-08 | Nevro Corp. | Leads having sidewall openings, and associated systems and methods |
US11172959B2 (en) | 2018-05-02 | 2021-11-16 | Boston Scientific Neuromodulation Corporation | Long, flexible sheath and lead blank and systems and methods of making and using |
EP3790623B1 (en) | 2018-05-11 | 2023-07-05 | Boston Scientific Neuromodulation Corporation | Connector assembly for an electrical stimulation system |
US10906702B2 (en) | 2018-10-02 | 2021-02-02 | Sulzer Mixpac Ag | Cartridge, method of manufacturing a cartridge, dispensing assembly and method of assembling a dispensing assembly |
BR112021005504A8 (en) | 2018-10-02 | 2023-03-21 | Sulzer Mixpac Ag | CARTRIDGE, METHOD OF MANUFACTURING A CARTRIDGE, DISPENSING ASSEMBLY AND METHOD FOR ASSEMBLING A DISPENSING ASSEMBLY |
US10870127B2 (en) | 2018-10-02 | 2020-12-22 | Sulzer Mixpac Ag | Cartridge for a mixing and dispensing system |
US11167128B2 (en) | 2018-11-16 | 2021-11-09 | Boston Scientific Neuromodulation Corporation | Directional electrical stimulation leads, systems and methods for spinal cord stimulation |
US11458300B2 (en) | 2018-12-28 | 2022-10-04 | Heraeus Medical Components Llc | Overmolded segmented electrode |
US11357992B2 (en) | 2019-05-03 | 2022-06-14 | Boston Scientific Neuromodulation Corporation | Connector assembly for an electrical stimulation system and methods of making and using |
Citations (89)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3333045A (en) * | 1965-07-20 | 1967-07-25 | Gen Electric | Body implantable electrical conductor |
US3367339A (en) * | 1964-10-09 | 1968-02-06 | Robert W. Sessions | Implantable nerve stimulating electrode and lead |
US3416534A (en) * | 1966-04-11 | 1968-12-17 | Gen Electric | Body organ electrode |
US3596662A (en) * | 1968-09-04 | 1971-08-03 | Medtronic Inc | Electrode for cardiac stimulator |
US3825015A (en) * | 1972-12-14 | 1974-07-23 | American Optical Corp | Single catheter for atrial and ventricular stimulation |
US4062150A (en) * | 1975-09-10 | 1977-12-13 | Hitachi, Ltd. | Centerless grinding method and device using same |
US4161952A (en) * | 1977-11-01 | 1979-07-24 | Mieczyslaw Mirowski | Wound wire catheter cardioverting electrode |
US4194323A (en) * | 1978-11-30 | 1980-03-25 | Combustion Engineering, Inc. | Centerless grinder |
US4285347A (en) * | 1979-07-25 | 1981-08-25 | Cordis Corporation | Stabilized directional neural electrode lead |
US4369791A (en) * | 1979-10-01 | 1983-01-25 | Medtronic, Inc. | Body implantable electrode |
US4374527A (en) * | 1978-07-19 | 1983-02-22 | Medtronic, Inc. | Body stimulation lead |
US4379462A (en) * | 1980-10-29 | 1983-04-12 | Neuromed, Inc. | Multi-electrode catheter assembly for spinal cord stimulation |
US4432377A (en) * | 1982-01-29 | 1984-02-21 | Medtronic, Inc. | Biomedical lead with ring electrode and method of making same |
US4437474A (en) * | 1982-07-16 | 1984-03-20 | Cordis Corporation | Method for making multiconductor coil and the coil made thereby |
US4458695A (en) * | 1982-07-16 | 1984-07-10 | Cordis Corporation | Multipolar electrode assembly for pacing lead |
US4469104A (en) * | 1982-07-16 | 1984-09-04 | Cordis Corporation | Multipolar connector for pacing lead |
US4480370A (en) * | 1982-06-07 | 1984-11-06 | Loevinger Richard P | Heated railroad tank car |
US4485268A (en) * | 1983-06-13 | 1984-11-27 | Minnesota Mining And Manufacturing | Sealing device for an electrical connector and method therefor |
US4498482A (en) * | 1979-12-13 | 1985-02-12 | Medtronic, Inc. | Transvenous pacing lead having improved stylet |
US4507896A (en) * | 1982-11-30 | 1985-04-02 | Energy Adaptive Grinding, Inc. | Centerless grinding systems |
US4514589A (en) * | 1981-09-03 | 1985-04-30 | Heraeus Quarschmelze Gmbh | Electrode connecting cable for cardiac pacemaker |
US4513540A (en) * | 1983-07-11 | 1985-04-30 | Ex-Cell-O Corporation | Grinding machine with CNC pivotable workhead |
US4549556A (en) * | 1982-12-08 | 1985-10-29 | Cordis Corporation | Implantable lead |
US4558537A (en) * | 1984-01-10 | 1985-12-17 | Taft-Peirce Supfina Machine Company, Inc. | Centerless honing machines having automatic size control |
US4559951A (en) * | 1982-11-29 | 1985-12-24 | Cardiac Pacemakers, Inc. | Catheter assembly |
US4572605A (en) * | 1984-08-09 | 1986-02-25 | Medtronic, Inc. | Injection molded in-line connector assembly for bipolar leads |
US4580368A (en) * | 1982-11-30 | 1986-04-08 | Energy Adaptive Grinding, Inc. | Centerless and center-type grinding systems |
US4592372A (en) * | 1984-05-22 | 1986-06-03 | Cordis Corporation | Pacing/sensing electrode sleeve and method of forming same |
US4608986A (en) * | 1984-10-01 | 1986-09-02 | Cordis Corporation | Pacing lead with straight wire conductors |
US4651751A (en) * | 1982-10-14 | 1987-03-24 | American Hospital Supply Corporation | Guiding catheter and method of use |
US4664120A (en) * | 1986-01-22 | 1987-05-12 | Cordis Corporation | Adjustable isodiametric atrial-ventricular pervenous lead |
US4699157A (en) * | 1985-08-27 | 1987-10-13 | Electro-Catheter Corporation | Pacing catheter and method of making same |
US4934049A (en) * | 1989-07-07 | 1990-06-19 | Medtronic, Inc. | Method for fabrication of a medical electrode |
US4947866A (en) * | 1988-02-16 | 1990-08-14 | Medtronic, Inc. | Medical electrical lead |
US5001825A (en) * | 1988-11-03 | 1991-03-26 | Cordis Corporation | Catheter guidewire fabrication method |
US5121754A (en) * | 1990-08-21 | 1992-06-16 | Medtronic, Inc. | Lateral displacement percutaneously inserted epidural lead |
US5267564A (en) * | 1991-06-14 | 1993-12-07 | Siemens Pacesetter, Inc. | Pacemaker lead for sensing a physiologic parameter of the body |
US5318572A (en) * | 1992-06-02 | 1994-06-07 | Siemens Pacesetter, Inc. | High efficiency tissue stimulating and signal sensing electrode |
US5330521A (en) * | 1992-06-29 | 1994-07-19 | Cohen Donald M | Low resistance implantable electrical leads |
US5374285A (en) * | 1992-07-31 | 1994-12-20 | Aries S.R.L. | Spinal electrode catheter |
US5387233A (en) * | 1993-01-11 | 1995-02-07 | Incontrol, Inc. | Intravenous cardiac lead with improved fixation and method |
US5409461A (en) * | 1993-09-28 | 1995-04-25 | Becton Dickinson And Company | Catheter introducer assembly with needle shielding device |
US5417208A (en) * | 1993-10-12 | 1995-05-23 | Arrow International Investment Corp. | Electrode-carrying catheter and method of making same |
US5458629A (en) * | 1994-02-18 | 1995-10-17 | Medtronic, Inc. | Implantable lead ring electrode and method of making |
US5466253A (en) * | 1993-04-27 | 1995-11-14 | Pacesetter, Inc. | Crush resistant multi-conductor lead body |
US5483022A (en) * | 1994-04-12 | 1996-01-09 | Ventritex, Inc. | Implantable conductor coil formed from cabled composite wire |
US5524338A (en) * | 1991-10-22 | 1996-06-11 | Pi Medical Corporation | Method of making implantable microelectrode |
US5545708A (en) * | 1993-07-14 | 1996-08-13 | Becton, Dickinson And Company | Thermoplastic polyurethane method of making same and forming a medical article therefrom |
US5555618A (en) * | 1993-10-12 | 1996-09-17 | Arrow International Investment Corp. | Method of making electrode-carrying catheter |
US5562722A (en) * | 1994-03-14 | 1996-10-08 | Medical Evaluation Devices & Instruments Corp. | Multiple electrode catheter |
US5571161A (en) * | 1995-04-12 | 1996-11-05 | Starksen; Niel F. | Apparatus and method for implanting electrical leads in the heart |
US5588432A (en) * | 1988-03-21 | 1996-12-31 | Boston Scientific Corporation | Catheters for imaging, sensing electrical potentials, and ablating tissue |
US5613899A (en) * | 1995-06-05 | 1997-03-25 | Southern Carbide Specialists, Inc. | Centerless ceramic ferrule grinder |
US5630826A (en) * | 1990-08-20 | 1997-05-20 | Sastri; Suri A. | Tubular surgical cutting instruments with coating |
US5643051A (en) * | 1995-06-16 | 1997-07-01 | The University Of Connecticut | Centerless grinding process and apparatus therefor |
US5667432A (en) * | 1993-08-24 | 1997-09-16 | Rollomatic S.A. | Grinding machine |
US5733322A (en) * | 1995-05-23 | 1998-03-31 | Medtronic, Inc. | Positive fixation percutaneous epidural neurostimulation lead |
US5746644A (en) * | 1996-02-08 | 1998-05-05 | Royal Master Grinders, Inc. | Centerless grinder assembly and method of operating the same |
US5772864A (en) * | 1996-02-23 | 1998-06-30 | Meadox Medicals, Inc. | Method for manufacturing implantable medical devices |
US5788558A (en) * | 1995-11-13 | 1998-08-04 | Localmed, Inc. | Apparatus and method for polishing lumenal prostheses |
US5796044A (en) * | 1997-02-10 | 1998-08-18 | Medtronic, Inc. | Coiled wire conductor insulation for biomedical lead |
US5797903A (en) * | 1996-04-12 | 1998-08-25 | Ep Technologies, Inc. | Tissue heating and ablation systems and methods using porous electrode structures with electrically conductive surfaces |
US5827272A (en) * | 1995-08-07 | 1998-10-27 | Medtronic Cardiorhythm | Simplified torquing electrode catheter |
US5830213A (en) * | 1996-04-12 | 1998-11-03 | Ep Technologies, Inc. | Systems for heating and ablating tissue using multifunctional electrode structures |
US5840076A (en) * | 1996-04-12 | 1998-11-24 | Ep Technologies, Inc. | Tissue heating and ablation systems and methods using electrode structures with distally oriented porous regions |
US5843148A (en) * | 1996-09-27 | 1998-12-01 | Medtronic, Inc. | High resolution brain stimulation lead and method of use |
US5846239A (en) * | 1996-04-12 | 1998-12-08 | Ep Technologies, Inc. | Tissue heating and ablation systems and methods using segmented porous electrode structures |
US5851222A (en) * | 1997-04-30 | 1998-12-22 | Medtronic, Inc. | Implantable medical device |
US5853652A (en) * | 1993-10-29 | 1998-12-29 | Medtronic, Inc. | Method of manufacturing a medical electrical lead |
US5865667A (en) * | 1996-05-22 | 1999-02-02 | Rollomatic S.A. | Grinding machine |
US5868736A (en) * | 1996-04-12 | 1999-02-09 | Ep Technologies, Inc. | Systems and methods to control tissue heating or ablation with porous electrode structures |
US5879348A (en) * | 1996-04-12 | 1999-03-09 | Ep Technologies, Inc. | Electrode structures formed from flexible, porous, or woven materials |
US5897584A (en) * | 1996-10-22 | 1999-04-27 | Medtronic, Inc. | Torque transfer device for temporary transvenous endocardial lead |
US5897566A (en) * | 1996-07-15 | 1999-04-27 | Shturman Cardiology Systems, Inc. | Rotational atherectomy device |
US5910129A (en) * | 1996-12-19 | 1999-06-08 | Ep Technologies, Inc. | Catheter distal assembly with pull wires |
US5916213A (en) * | 1997-02-04 | 1999-06-29 | Medtronic, Inc. | Systems and methods for tissue mapping and ablation |
US5924915A (en) * | 1997-08-18 | 1999-07-20 | Wachtler; William R. | Hand held self aligning shaft grinder |
US5957966A (en) * | 1998-02-18 | 1999-09-28 | Intermedics Inc. | Implantable cardiac lead with multiple shape memory polymer structures |
US5961513A (en) * | 1996-01-19 | 1999-10-05 | Ep Technologies, Inc. | Tissue heating and ablation systems and methods using porous electrode structures |
US6002969A (en) * | 1998-08-05 | 1999-12-14 | Intermedics Inc. | Cardiac lead with shape-memory structure |
US6004291A (en) * | 1988-02-29 | 1999-12-21 | Scimed Life Systems, Inc. | Intravascular catheter with distal guide wire lumen and transition |
US6033720A (en) * | 1995-06-30 | 2000-03-07 | Meadox Medicals, Inc. | Guidewire having a coated tip |
US6048329A (en) * | 1996-12-19 | 2000-04-11 | Ep Technologies, Inc. | Catheter distal assembly with pull wires |
US6071278A (en) * | 1996-02-28 | 2000-06-06 | Ep Technologies, Inc. | Tissue heating and ablation systems and methods using porous electrode structures with specified electrical resistivities |
US6099526A (en) * | 1996-01-19 | 2000-08-08 | Ep Technologies, Inc. | Electrode structure including hydrophilic material |
US6185463B1 (en) * | 1997-05-01 | 2001-02-06 | Medtronic, Inc. | Implantable short resistant lead |
US6203525B1 (en) * | 1996-12-19 | 2001-03-20 | Ep Technologies, Inc. | Catheterdistal assembly with pull wires |
US6236892B1 (en) * | 1999-10-07 | 2001-05-22 | Claudio A. Feler | Spinal cord stimulation lead |
US6253111B1 (en) * | 1998-03-30 | 2001-06-26 | Pacesetter, Inc. | Multi-conductor lead |
Family Cites Families (55)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3378673A (en) * | 1965-10-18 | 1968-04-16 | Thomas O. Hopper | Electrically heated hose assembly |
US3769984A (en) * | 1971-03-11 | 1973-11-06 | Sherwood Medical Ind Inc | Pacing catheter with frictional fit lead attachment |
US3760812A (en) * | 1971-03-19 | 1973-09-25 | Univ Minnesota | Implantable spiral wound stimulation electrodes |
US4280511A (en) * | 1980-02-25 | 1981-07-28 | Medtronic, Inc. | Ring electrode for pacing lead and process of making same |
US4381014A (en) * | 1980-10-10 | 1983-04-26 | Medtronic, Inc. | Ring electrode for pacing lead and method of making same |
US4355646A (en) * | 1980-11-26 | 1982-10-26 | Medtronic, Inc. | Transvenous defibrillating lead |
US4374627A (en) * | 1981-01-13 | 1983-02-22 | Friedman Michael N | Binder for perforated sheets or the like |
US4444195A (en) * | 1981-11-02 | 1984-04-24 | Cordis Corporation | Cardiac lead having multiple ring electrodes |
US4484586A (en) * | 1982-05-27 | 1984-11-27 | Berkley & Company, Inc. | Hollow conductive medical tubing |
US4764324A (en) * | 1983-12-12 | 1988-08-16 | Warren Burnham | Method of making a catheter |
US4995389A (en) * | 1985-12-16 | 1991-02-26 | Telectronics Pacing Systems, Inc. | Multielectrode quick connect cardiac pacing lead connector assembly |
EP0293499B1 (en) | 1987-06-01 | 1993-09-01 | Siemens-Elema AB | Implantable multi-pole coaxial lead |
EP0312495A3 (en) * | 1987-10-16 | 1989-08-30 | Institut Straumann Ag | Electrical cable for carrying out at least one stimulation and/or measurement in a human or animal body |
US5216045A (en) * | 1988-01-13 | 1993-06-01 | The Dow Chemical Company | Controlled film build epoxy coatings using glycidyl ethers of oxyalkylated aromatic and cycloaliphatic diols |
US4860446A (en) | 1988-02-16 | 1989-08-29 | Medtronic, Inc. | Medical electrical lead and method of manufacture |
US5016646A (en) * | 1988-11-29 | 1991-05-21 | Telectronics, N.V. | Thin electrode lead and connections |
US5143013A (en) * | 1991-04-29 | 1992-09-01 | Outboard Marine Corporation | Center console including storage locker |
DE4120446A1 (en) * | 1991-06-20 | 1992-12-24 | Linde Ag | METHOD AND DEVICE FOR THE SYNTHESIS OF BUTINDIOL |
US5246016A (en) * | 1991-11-08 | 1993-09-21 | Baxter International Inc. | Transport catheter and multiple probe analysis method |
US5683366A (en) * | 1992-01-07 | 1997-11-04 | Arthrocare Corporation | System and method for electrosurgical tissue canalization |
US5231996A (en) * | 1992-01-28 | 1993-08-03 | Medtronic, Inc. | Removable endocardial lead |
US5334169A (en) * | 1992-05-11 | 1994-08-02 | American Interventional Technologies, Inc. | Reinforced catheter with thin monolithic walls |
US5330522A (en) * | 1992-12-29 | 1994-07-19 | Siemens Pacesetter, Inc. | Ring electrode for a multilumen lead and method of constructing a multilumen lead |
US5476495A (en) * | 1993-03-16 | 1995-12-19 | Ep Technologies, Inc. | Cardiac mapping and ablation systems |
US5840031A (en) * | 1993-07-01 | 1998-11-24 | Boston Scientific Corporation | Catheters for imaging, sensing electrical potentials and ablating tissue |
US5439485A (en) * | 1993-09-24 | 1995-08-08 | Ventritex, Inc. | Flexible defibrillation electrode of improved construction |
US5458659A (en) * | 1993-10-20 | 1995-10-17 | Florida Power Corporation | Desulfurization of carbonaceous fuels |
US5433742A (en) * | 1993-11-19 | 1995-07-18 | Willis; Allan | Conductive adhesive band for cathether electrode |
US5857997A (en) * | 1994-11-14 | 1999-01-12 | Heart Rhythm Technologies, Inc. | Catheter for electrophysiological procedures |
US5957910A (en) * | 1995-03-14 | 1999-09-28 | Mallinckrodt Medical, Inc. | Catheters with reinforced filaments |
DE69606845T2 (en) | 1995-04-28 | 2000-06-15 | Target Therapeutics, Inc. | High performance catheter with braided element |
US6824553B1 (en) * | 1995-04-28 | 2004-11-30 | Target Therapeutics, Inc. | High performance braided catheter |
US5762631A (en) * | 1995-07-14 | 1998-06-09 | Localmed, Inc. | Method and system for reduced friction introduction of coaxial catheters |
US5772693A (en) * | 1996-02-09 | 1998-06-30 | Cardiac Control Systems, Inc. | Single preformed catheter configuration for a dual-chamber pacemaker system |
US5824026A (en) * | 1996-06-12 | 1998-10-20 | The Spectranetics Corporation | Catheter for delivery of electric energy and a process for manufacturing same |
US5938596A (en) * | 1997-03-17 | 1999-08-17 | Medtronic, Inc. | Medical electrical lead |
DE69801001T2 (en) | 1997-04-21 | 2002-03-14 | Medtronic, Inc. | MEDICAL ELECTRICAL LINE |
US5951539A (en) * | 1997-06-10 | 1999-09-14 | Target Therpeutics, Inc. | Optimized high performance multiple coil spiral-wound vascular catheter |
US6324415B1 (en) * | 1997-07-30 | 2001-11-27 | Intermedics Inc. | Cardiac lead with minimized inside diameter of sleeve |
US5928277A (en) * | 1998-02-19 | 1999-07-27 | Medtronic, Inc. | One piece defibrillation lead circuit |
US6018684A (en) * | 1998-07-30 | 2000-01-25 | Cardiac Pacemakers, Inc. | Slotted pacing/shocking electrode |
US6208881B1 (en) * | 1998-10-20 | 2001-03-27 | Micropure Medical, Inc. | Catheter with thin film electrodes and method for making same |
US6181971B1 (en) * | 1998-12-09 | 2001-01-30 | Pacesetter, Inc. | Joining conductor cables and electrodes on a multi-lumen lead body |
US6216045B1 (en) * | 1999-04-26 | 2001-04-10 | Advanced Neuromodulation Systems, Inc. | Implantable lead and method of manufacture |
US6213995B1 (en) * | 1999-08-31 | 2001-04-10 | Phelps Dodge High Performance Conductors Of Sc And Ga, Inc. | Flexible tubing with braided signal transmission elements |
US6363286B1 (en) * | 1999-09-24 | 2002-03-26 | Cardiac Pacemakers, Inc. | High impedance electrode assembly |
US6295476B1 (en) * | 1999-11-01 | 2001-09-25 | Medtronic, Inc. | Medical lead conductor fracture visualization method and apparatus |
JP3915862B2 (en) * | 2000-02-09 | 2007-05-16 | テルモ株式会社 | catheter |
US6366820B1 (en) * | 2000-03-01 | 2002-04-02 | Pacesetter, Inc. | Interconnection technique between a cable conductor and an electrode of an implantable medical device |
US6477427B1 (en) * | 2000-03-31 | 2002-11-05 | Medtronic Inc. | Implantable stimulation lead and method of manufacture |
US7149585B2 (en) * | 2001-03-30 | 2006-12-12 | Micronet Medical, Inc. | Lead body and method of lead body construction |
US6540076B1 (en) * | 2001-05-17 | 2003-04-01 | Day International, Inc. | Dispensing carton for metal-backed printing blanket |
US6701191B2 (en) * | 2001-05-30 | 2004-03-02 | Cardiac Pacemakers, Inc. | Lead having composite tubing |
US7047084B2 (en) * | 2002-11-20 | 2006-05-16 | Advanced Neuromodulation Systems, Inc. | Apparatus for directionally stimulating nerve tissue |
US7395116B2 (en) * | 2004-08-19 | 2008-07-01 | Medtronic, Inc. | Lead body-to-connector transition zone |
-
1999
- 1999-04-26 US US09/299,702 patent/US6216045B1/en not_active Expired - Lifetime
-
2000
- 2000-02-16 WO PCT/US2000/003920 patent/WO2000064530A1/en active Application Filing
- 2000-02-16 IL IL14520800A patent/IL145208A0/en unknown
- 2000-02-16 AU AU40015/00A patent/AU774533B2/en not_active Ceased
- 2000-02-16 JP JP2000613517A patent/JP2002541993A/en active Pending
- 2000-02-16 EP EP00919307A patent/EP1171192B1/en not_active Expired - Lifetime
-
2001
- 2001-01-12 US US09/760,437 patent/US20010023368A1/en not_active Abandoned
-
2002
- 2002-01-09 US US10/042,992 patent/US6981314B2/en not_active Expired - Fee Related
-
2004
- 2004-09-30 AU AU2004216639A patent/AU2004216639A1/en not_active Abandoned
-
2005
- 2005-03-11 US US11/077,884 patent/US20050138791A1/en not_active Abandoned
- 2005-03-11 US US11/078,788 patent/US20050192655A1/en not_active Abandoned
- 2005-03-11 US US11/078,878 patent/US20050138792A1/en not_active Abandoned
- 2005-08-03 US US11/196,590 patent/US7047627B2/en not_active Expired - Lifetime
-
2009
- 2009-12-04 US US12/631,321 patent/US8316537B2/en not_active Expired - Lifetime
-
2012
- 2012-09-14 US US13/617,187 patent/US8671566B2/en not_active Expired - Fee Related
Patent Citations (95)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3367339A (en) * | 1964-10-09 | 1968-02-06 | Robert W. Sessions | Implantable nerve stimulating electrode and lead |
US3333045A (en) * | 1965-07-20 | 1967-07-25 | Gen Electric | Body implantable electrical conductor |
US3416534A (en) * | 1966-04-11 | 1968-12-17 | Gen Electric | Body organ electrode |
US3596662A (en) * | 1968-09-04 | 1971-08-03 | Medtronic Inc | Electrode for cardiac stimulator |
US3825015A (en) * | 1972-12-14 | 1974-07-23 | American Optical Corp | Single catheter for atrial and ventricular stimulation |
US4062150A (en) * | 1975-09-10 | 1977-12-13 | Hitachi, Ltd. | Centerless grinding method and device using same |
US4161952A (en) * | 1977-11-01 | 1979-07-24 | Mieczyslaw Mirowski | Wound wire catheter cardioverting electrode |
US4374527A (en) * | 1978-07-19 | 1983-02-22 | Medtronic, Inc. | Body stimulation lead |
US4194323A (en) * | 1978-11-30 | 1980-03-25 | Combustion Engineering, Inc. | Centerless grinder |
US4285347A (en) * | 1979-07-25 | 1981-08-25 | Cordis Corporation | Stabilized directional neural electrode lead |
US4369791A (en) * | 1979-10-01 | 1983-01-25 | Medtronic, Inc. | Body implantable electrode |
US4498482A (en) * | 1979-12-13 | 1985-02-12 | Medtronic, Inc. | Transvenous pacing lead having improved stylet |
US4379462A (en) * | 1980-10-29 | 1983-04-12 | Neuromed, Inc. | Multi-electrode catheter assembly for spinal cord stimulation |
US4514589A (en) * | 1981-09-03 | 1985-04-30 | Heraeus Quarschmelze Gmbh | Electrode connecting cable for cardiac pacemaker |
US4432377A (en) * | 1982-01-29 | 1984-02-21 | Medtronic, Inc. | Biomedical lead with ring electrode and method of making same |
US4480370A (en) * | 1982-06-07 | 1984-11-06 | Loevinger Richard P | Heated railroad tank car |
US4437474A (en) * | 1982-07-16 | 1984-03-20 | Cordis Corporation | Method for making multiconductor coil and the coil made thereby |
US4458695A (en) * | 1982-07-16 | 1984-07-10 | Cordis Corporation | Multipolar electrode assembly for pacing lead |
US4469104A (en) * | 1982-07-16 | 1984-09-04 | Cordis Corporation | Multipolar connector for pacing lead |
US4651751A (en) * | 1982-10-14 | 1987-03-24 | American Hospital Supply Corporation | Guiding catheter and method of use |
US4559951A (en) * | 1982-11-29 | 1985-12-24 | Cardiac Pacemakers, Inc. | Catheter assembly |
US4507896A (en) * | 1982-11-30 | 1985-04-02 | Energy Adaptive Grinding, Inc. | Centerless grinding systems |
US4580368A (en) * | 1982-11-30 | 1986-04-08 | Energy Adaptive Grinding, Inc. | Centerless and center-type grinding systems |
US4549556A (en) * | 1982-12-08 | 1985-10-29 | Cordis Corporation | Implantable lead |
US4485268A (en) * | 1983-06-13 | 1984-11-27 | Minnesota Mining And Manufacturing | Sealing device for an electrical connector and method therefor |
US4513540A (en) * | 1983-07-11 | 1985-04-30 | Ex-Cell-O Corporation | Grinding machine with CNC pivotable workhead |
US4558537A (en) * | 1984-01-10 | 1985-12-17 | Taft-Peirce Supfina Machine Company, Inc. | Centerless honing machines having automatic size control |
US4592372A (en) * | 1984-05-22 | 1986-06-03 | Cordis Corporation | Pacing/sensing electrode sleeve and method of forming same |
US4572605A (en) * | 1984-08-09 | 1986-02-25 | Medtronic, Inc. | Injection molded in-line connector assembly for bipolar leads |
US4608986A (en) * | 1984-10-01 | 1986-09-02 | Cordis Corporation | Pacing lead with straight wire conductors |
US4699157A (en) * | 1985-08-27 | 1987-10-13 | Electro-Catheter Corporation | Pacing catheter and method of making same |
US4664120A (en) * | 1986-01-22 | 1987-05-12 | Cordis Corporation | Adjustable isodiametric atrial-ventricular pervenous lead |
US4947866A (en) * | 1988-02-16 | 1990-08-14 | Medtronic, Inc. | Medical electrical lead |
US6004291A (en) * | 1988-02-29 | 1999-12-21 | Scimed Life Systems, Inc. | Intravascular catheter with distal guide wire lumen and transition |
US5588432A (en) * | 1988-03-21 | 1996-12-31 | Boston Scientific Corporation | Catheters for imaging, sensing electrical potentials, and ablating tissue |
US5001825A (en) * | 1988-11-03 | 1991-03-26 | Cordis Corporation | Catheter guidewire fabrication method |
US4934049A (en) * | 1989-07-07 | 1990-06-19 | Medtronic, Inc. | Method for fabrication of a medical electrode |
US5630826A (en) * | 1990-08-20 | 1997-05-20 | Sastri; Suri A. | Tubular surgical cutting instruments with coating |
US5121754A (en) * | 1990-08-21 | 1992-06-16 | Medtronic, Inc. | Lateral displacement percutaneously inserted epidural lead |
US5267564A (en) * | 1991-06-14 | 1993-12-07 | Siemens Pacesetter, Inc. | Pacemaker lead for sensing a physiologic parameter of the body |
US5304219A (en) * | 1991-06-14 | 1994-04-19 | Siemens Pacesetter, Inc. | Multipolar in-line proximal connector assembly for an implantable stimulation device |
US5490323A (en) * | 1991-06-14 | 1996-02-13 | Pacesetter, Inc. | Method for making a body implantable sensor |
US5524338A (en) * | 1991-10-22 | 1996-06-11 | Pi Medical Corporation | Method of making implantable microelectrode |
US5318572A (en) * | 1992-06-02 | 1994-06-07 | Siemens Pacesetter, Inc. | High efficiency tissue stimulating and signal sensing electrode |
US5330521A (en) * | 1992-06-29 | 1994-07-19 | Cohen Donald M | Low resistance implantable electrical leads |
US5374285A (en) * | 1992-07-31 | 1994-12-20 | Aries S.R.L. | Spinal electrode catheter |
US5387233A (en) * | 1993-01-11 | 1995-02-07 | Incontrol, Inc. | Intravenous cardiac lead with improved fixation and method |
US5466253A (en) * | 1993-04-27 | 1995-11-14 | Pacesetter, Inc. | Crush resistant multi-conductor lead body |
US5545708A (en) * | 1993-07-14 | 1996-08-13 | Becton, Dickinson And Company | Thermoplastic polyurethane method of making same and forming a medical article therefrom |
US5667432A (en) * | 1993-08-24 | 1997-09-16 | Rollomatic S.A. | Grinding machine |
US5409461A (en) * | 1993-09-28 | 1995-04-25 | Becton Dickinson And Company | Catheter introducer assembly with needle shielding device |
US5555618A (en) * | 1993-10-12 | 1996-09-17 | Arrow International Investment Corp. | Method of making electrode-carrying catheter |
US5417208A (en) * | 1993-10-12 | 1995-05-23 | Arrow International Investment Corp. | Electrode-carrying catheter and method of making same |
US5853652A (en) * | 1993-10-29 | 1998-12-29 | Medtronic, Inc. | Method of manufacturing a medical electrical lead |
US5458629A (en) * | 1994-02-18 | 1995-10-17 | Medtronic, Inc. | Implantable lead ring electrode and method of making |
US5562722A (en) * | 1994-03-14 | 1996-10-08 | Medical Evaluation Devices & Instruments Corp. | Multiple electrode catheter |
US5483022A (en) * | 1994-04-12 | 1996-01-09 | Ventritex, Inc. | Implantable conductor coil formed from cabled composite wire |
US5571161A (en) * | 1995-04-12 | 1996-11-05 | Starksen; Niel F. | Apparatus and method for implanting electrical leads in the heart |
US5733322A (en) * | 1995-05-23 | 1998-03-31 | Medtronic, Inc. | Positive fixation percutaneous epidural neurostimulation lead |
US5613899A (en) * | 1995-06-05 | 1997-03-25 | Southern Carbide Specialists, Inc. | Centerless ceramic ferrule grinder |
US5643051A (en) * | 1995-06-16 | 1997-07-01 | The University Of Connecticut | Centerless grinding process and apparatus therefor |
US6033720A (en) * | 1995-06-30 | 2000-03-07 | Meadox Medicals, Inc. | Guidewire having a coated tip |
US6059738A (en) * | 1995-06-30 | 2000-05-09 | Meadox Medicals, Inc. | Guidewire having a coated tip |
US5827272A (en) * | 1995-08-07 | 1998-10-27 | Medtronic Cardiorhythm | Simplified torquing electrode catheter |
US5788558A (en) * | 1995-11-13 | 1998-08-04 | Localmed, Inc. | Apparatus and method for polishing lumenal prostheses |
US5961513A (en) * | 1996-01-19 | 1999-10-05 | Ep Technologies, Inc. | Tissue heating and ablation systems and methods using porous electrode structures |
US6099526A (en) * | 1996-01-19 | 2000-08-08 | Ep Technologies, Inc. | Electrode structure including hydrophilic material |
US5746644A (en) * | 1996-02-08 | 1998-05-05 | Royal Master Grinders, Inc. | Centerless grinder assembly and method of operating the same |
US5772864A (en) * | 1996-02-23 | 1998-06-30 | Meadox Medicals, Inc. | Method for manufacturing implantable medical devices |
US6071278A (en) * | 1996-02-28 | 2000-06-06 | Ep Technologies, Inc. | Tissue heating and ablation systems and methods using porous electrode structures with specified electrical resistivities |
US5846239A (en) * | 1996-04-12 | 1998-12-08 | Ep Technologies, Inc. | Tissue heating and ablation systems and methods using segmented porous electrode structures |
US5797903A (en) * | 1996-04-12 | 1998-08-25 | Ep Technologies, Inc. | Tissue heating and ablation systems and methods using porous electrode structures with electrically conductive surfaces |
US5830213A (en) * | 1996-04-12 | 1998-11-03 | Ep Technologies, Inc. | Systems for heating and ablating tissue using multifunctional electrode structures |
US5868736A (en) * | 1996-04-12 | 1999-02-09 | Ep Technologies, Inc. | Systems and methods to control tissue heating or ablation with porous electrode structures |
US5840076A (en) * | 1996-04-12 | 1998-11-24 | Ep Technologies, Inc. | Tissue heating and ablation systems and methods using electrode structures with distally oriented porous regions |
US5879348A (en) * | 1996-04-12 | 1999-03-09 | Ep Technologies, Inc. | Electrode structures formed from flexible, porous, or woven materials |
US5865667A (en) * | 1996-05-22 | 1999-02-02 | Rollomatic S.A. | Grinding machine |
US5897566A (en) * | 1996-07-15 | 1999-04-27 | Shturman Cardiology Systems, Inc. | Rotational atherectomy device |
US5843148A (en) * | 1996-09-27 | 1998-12-01 | Medtronic, Inc. | High resolution brain stimulation lead and method of use |
US5897584A (en) * | 1996-10-22 | 1999-04-27 | Medtronic, Inc. | Torque transfer device for temporary transvenous endocardial lead |
US5910129A (en) * | 1996-12-19 | 1999-06-08 | Ep Technologies, Inc. | Catheter distal assembly with pull wires |
US6203525B1 (en) * | 1996-12-19 | 2001-03-20 | Ep Technologies, Inc. | Catheterdistal assembly with pull wires |
US6048329A (en) * | 1996-12-19 | 2000-04-11 | Ep Technologies, Inc. | Catheter distal assembly with pull wires |
US5916213A (en) * | 1997-02-04 | 1999-06-29 | Medtronic, Inc. | Systems and methods for tissue mapping and ablation |
US6068629A (en) * | 1997-02-04 | 2000-05-30 | Medtronic, Inc. | System and methods for tissue mapping and ablation |
US5796044A (en) * | 1997-02-10 | 1998-08-18 | Medtronic, Inc. | Coiled wire conductor insulation for biomedical lead |
US5871513A (en) * | 1997-04-30 | 1999-02-16 | Medtronic Inc. | Centerless ground feedthrough pin for an electrical power source in an implantable medical device |
US6076017A (en) * | 1997-04-30 | 2000-06-13 | Medtronic, Inc. | Method of centerless ground finishing of feedthrough pins for an implantable medical device |
US5851222A (en) * | 1997-04-30 | 1998-12-22 | Medtronic, Inc. | Implantable medical device |
US6185463B1 (en) * | 1997-05-01 | 2001-02-06 | Medtronic, Inc. | Implantable short resistant lead |
US5924915A (en) * | 1997-08-18 | 1999-07-20 | Wachtler; William R. | Hand held self aligning shaft grinder |
US5957966A (en) * | 1998-02-18 | 1999-09-28 | Intermedics Inc. | Implantable cardiac lead with multiple shape memory polymer structures |
US6253111B1 (en) * | 1998-03-30 | 2001-06-26 | Pacesetter, Inc. | Multi-conductor lead |
US6002969A (en) * | 1998-08-05 | 1999-12-14 | Intermedics Inc. | Cardiac lead with shape-memory structure |
US6236892B1 (en) * | 1999-10-07 | 2001-05-22 | Claudio A. Feler | Spinal cord stimulation lead |
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Also Published As
Publication number | Publication date |
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AU2004216639A1 (en) | 2004-10-28 |
JP2002541993A (en) | 2002-12-10 |
AU4001500A (en) | 2000-11-10 |
US6216045B1 (en) | 2001-04-10 |
EP1171192A1 (en) | 2002-01-16 |
US8316537B2 (en) | 2012-11-27 |
US20050138792A1 (en) | 2005-06-30 |
US20020055765A1 (en) | 2002-05-09 |
US20050246005A1 (en) | 2005-11-03 |
IL145208A0 (en) | 2002-06-30 |
US8671566B2 (en) | 2014-03-18 |
WO2000064530A1 (en) | 2000-11-02 |
US20100077606A1 (en) | 2010-04-01 |
US6981314B2 (en) | 2006-01-03 |
EP1171192B1 (en) | 2011-06-29 |
AU774533B2 (en) | 2004-07-01 |
US20050138791A1 (en) | 2005-06-30 |
US20010023368A1 (en) | 2001-09-20 |
US20130167372A1 (en) | 2013-07-04 |
US7047627B2 (en) | 2006-05-23 |
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