WO2010059305A1 - Électrode repoussant les cellules comportant une surface structurée - Google Patents

Électrode repoussant les cellules comportant une surface structurée Download PDF

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Publication number
WO2010059305A1
WO2010059305A1 PCT/US2009/060219 US2009060219W WO2010059305A1 WO 2010059305 A1 WO2010059305 A1 WO 2010059305A1 US 2009060219 W US2009060219 W US 2009060219W WO 2010059305 A1 WO2010059305 A1 WO 2010059305A1
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WO
WIPO (PCT)
Prior art keywords
lead
structured surface
electrode
adhesion layer
coating
Prior art date
Application number
PCT/US2009/060219
Other languages
English (en)
Inventor
Torsten Scheuermann
Original Assignee
Cardiac Pacemakers, Inc.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Cardiac Pacemakers, Inc. filed Critical Cardiac Pacemakers, Inc.
Priority to EP09743985A priority Critical patent/EP2370150A1/fr
Priority to JP2011537451A priority patent/JP2012509140A/ja
Priority to AU2009317980A priority patent/AU2009317980A1/en
Publication of WO2010059305A1 publication Critical patent/WO2010059305A1/fr

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Classifications

    • 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
    • A61N1/0565—Electrode heads
    • 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
    • A61N1/057—Anchoring means; Means for fixing the head inside the heart
    • A61N2001/0578—Anchoring means; Means for fixing the head inside the heart having means for removal or extraction
    • 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

Definitions

  • This invention relates to body implantable medical devices, and more particularly, to implantable electrodes for sensing electrical impulses in body tissue or for delivering electrical stimulation pulses to an organ, for example, for pacing the heart.
  • Various types of medical electrical leads for use in cardiac rhythm management systems are known. Such leads are typically extended intravascularly to an implantation location within or on a patient's heart, and thereafter coupled to a pulse generator or other implantable device for sensing cardiac electrical activity, delivering therapeutic stimuli, and the like.
  • the leads are desirably highly flexible to accommodate natural patient movement, yet also constructed to have minimized profiles.
  • the leads are exposed to various external forces imposed, for example, by the human muscular and skeletal system, the pulse generator, other leads, and surgical instruments used during implantation and explantation procedures. There is a continuing need for improved lead designs.
  • the present invention in one embodiment, is a medical electrical lead comprising a flexible lead body defining at least one longitudinal lumen therethrough, a conducting wire extending through the at least one lumen, a connector coupled to the lead body for mechanically and electrically coupling the lead to an implantable pulse generator device, and an electrode.
  • the electrode includes an electrode body including a structured surface, and a conductive coating disposed on the structured surface.
  • the conductive coating is electrically coupled to the at least one conducting wire.
  • the structured surface has pillars.
  • the conductive coating has an adhesion layer disposed on the structured surface and an external coating disposed over the adhesion layer.
  • the present invention is a method of making an electrode for a medical electrical lead of the type having a flexible lead body and at least one electrical conducting wire therein.
  • the method comprises forming an electrode body, forming a structured surface on the electrode body, applying an adhesion layer to the structured surface, and applying a conductive external coating to the adhesion layer.
  • the present invention is an electrode for use on an implantable medical electrical lead having at least one conductive member.
  • the electrode comprises an electrode body comprising a structured surface and a conductive coating disposed on the structured surface.
  • the conductive coating has a surface topography configured to exhibit hydrophobic behavior, and is configured to be electrically coupled to the lead conductive wire.
  • FIG. 1 is a schematic drawing of a cardiac rhythm management system including a pulse generator coupled to a pair of medical electrical leads deployed in a patient's heart, according to one embodiment.
  • FIG. 2 is a perspective view of one of the leads shown in FIG. 1 , according to one embodiment.
  • FIG. 3A is a schematic drawing of an electrode having a body and a structured surface and conductive coating, according to one embodiment.
  • FIG. 3B is another, expanded view of the schematic drawing of the electrode of FIG. 3A, according to one embodiment.
  • FIG. 4 is an image of exemplary pillar-like structures of a structured surface, according to one embodiment.
  • FIG. 5 is an image of exemplary rice grain structures of an external coating, according to one embodiment.
  • FIG. 6 is a cross-sectional view of an electrode, according to one embodiment.
  • the various embodiments disclosed herein relate to a medical electrical lead having an electrode having a structured surface and a conductive coating and related methods of making the lead.
  • the leads according to the various embodiments of the present invention are suitable for sensing intrinsic electrical activity and/or applying therapeutic electrical stimuli to a patient.
  • Exemplary applications include, without limitation, cardiac rhythm management (CRM) systems and neurostimulation systems.
  • CRM cardiac rhythm management
  • the medical electrical leads according to embodiments of the invention can be endocardial leads configured to be partially implanted within one or more chambers of the heart so as to sense electrical activity of the heart and apply a therapeutic electrical stimulus to the cardiac tissue within the heart.
  • leads formed according to embodiments of the present invention may be particularly suitable for placement in a coronary vein adjacent to the left side of the heart so as to facilitate bi-ventricular pacing in a CRT or CRT-D system. Still additionally, leads formed according to embodiments of the present invention may be configured to be secured to an exterior surface of the heart (i.e., as epicardial leads). FIG.
  • FIG. 1 is a schematic drawing of a cardiac rhythm management system 10 including a pulse generator 12 coupled to a pair of medical electrical leads 14, 16 deployed in a patient's heart 18, which includes a right atrium 20 and a right ventricle 22, a left atrium 24 and a left ventricle 26, a coronary sinus ostium 28 in the right atrium 20, a coronary sinus 30, and various coronary veins including an exemplary branch vessel 32 off of the coronary sinus 30.
  • lead 14 includes a proximal portion 42 and a distal portion 36, which as shown is guided through the right atrium 20, the coronary sinus ostium 28 and the coronary sinus 30, and into the branch vessel 32 of the coronary sinus 30.
  • the distal portion 36 further includes a distal end 38 and an electrode 40 both positioned within the branch vessel 32.
  • the illustrated position of the lead 14 may be used for delivering a pacing and/or defibrillation stimulus to the left side of the heart 18. Additionally, it will be appreciated that the lead 14 may also be partially deployed in other regions of the coronary venous system, such as in the great cardiac vein or other branch vessels for providing therapy to the left side or right side of the heart 18.
  • the electrode 40 is a relatively small, low voltage electrode configured for sensing intrinsic cardiac electrical rhythms and/or delivering relatively low voltage pacing stimuli to the left ventricle 26 from within the branch coronary vein 32.
  • the lead 14 can include additional pace/sense electrodes for multi-polar pacing and/or for providing selective pacing site locations.
  • the lead 16 includes a proximal portion 34 and a distal portion 44 implanted in the right ventricle 22.
  • the CRM system 10 may include still additional leads, e.g., a lead implanted in the right atrium 20.
  • the distal portion 44 further includes a flexible, high voltage electrode 46, a relatively low-voltage ring electrode 48, and a low voltage tip electrode 50 all implanted in the right ventricle 22 in the illustrated embodiment.
  • the high voltage electrode 46 has a relatively large surface area compared to the ring electrode 48 and the tip electrode 50, and is thus configured for delivering relatively high voltage electrical stimulus to the cardiac tissue for defibrillation/cardioversion therapy, while the ring and tip electrodes 48, 50 are configured as relatively low voltage pace/sense electrodes.
  • the electrodes 48, 50 provide the lead 16 with bi-polar pace/sense capabilities.
  • the lead 16 includes additional defibrillation/cardioversion and/or additional pace/sense electrodes positioned along the lead 16 so as to provide multi-polar defibrillation/cardioversion capabilities.
  • the lead 16 includes a proximal high voltage electrode in addition to the electrode 46 positioned along the lead 16 such that it is located in the right atrium 20 (and/or superior vena cava) when implanted.
  • additional electrode configurations can be utilized with the lead 16. In short, any electrode configuration can be employed in the lead 16 without departing from the intended scope of the present invention.
  • the pulse generator 12 is typically implanted subcutaneously within an implantation location or pocket in the patient's chest or abdomen.
  • the pulse generator 12 may be any implantable medical device known in the art or later developed, for delivering an electrical therapeutic stimulus to the patient.
  • the pulse generator 12 is a pacemaker, an implantable cardiac defibrillator, a cardiac resynchronization (CRT) device configured for bi-venthcular pacing, and/or includes combinations of pacing, CRT, and defibrillation capabilities.
  • CTR cardiac resynchronization
  • FIG. 2 is a perspective view of the lead 16 shown in FIG 1.
  • the lead 16 is adapted to deliver electrical pulses to stimulate a heart and/or for receiving electrical pulses to monitor the heart.
  • the lead 16 includes an elongated lead body 52, which may be formed from any polymeric material such as polyamide, polycarbonate, silicone rubber, or the like.
  • the lead body 52 is not polymeric and instead is formed from a metal material such as copper, silver, aluminum, stainless steel (such as, for example, Grade 316L stainless steel), nitinol, CoCr, FePt, or any other metal material that can be used for a lead body.
  • the polymeric material is stable to a temperature of at least about 100° Celsius. That is, the polymeric material is configured to maintain its integrity up to at least about 100° C. In one aspect, this heat stability allows the polymeric material to withstand the texturing or structuring and coating processes described below. In alternative embodiments in which the lead body is non- polymeric, the metal materials discussed above can withstand much higher temperatures than polymeric materials and thus are stable to temperatures of at least 200° Celsius.
  • the lead 16 further includes a connector 54 operatively associated with the proximal end of the lead body 52.
  • the connector 54 is configured to mechanically and electrically couple the lead 16 to the pulse generator 12, and may be of any standard type, size or configuration.
  • the connector 54 is electrically and mechanically connected to the electrodes 46, 48, 50 by way of one or more conducting wires (not shown) within the lead body 52.
  • the conducting wires utilized may take on any configuration providing the necessary functionality.
  • the conducting wires coupling the electrodes 48 and/or 50 to the connector 54 (and thus, to the pulse generator 12) may be coiled conductors defining an internal lumen for receiving a stylet or guidewire for lead delivery.
  • the conducting wire to the high voltage electrode 46 may be a multi-strand cable conductor.
  • one or more of the electrodes 46, 48, 50 e.g., the high voltage electrode 46, includes a structured surface configured to exhibit hydrophobic qualities.
  • the hydrophobic qualities advantageously inhibit tissue in growth and/or attachment to the electrode surface.
  • the electrode configurations according to various embodiments of the present invention provide alternatives to existing techniques for inhibiting tissue adhesion and in growth to electrode surfaces, e.g., ePTFE coatings or wraps.
  • an electrode 60 (similar to the electrode in FIGS. 1 and 2) has a polymeric body 62 with a structured surface 64, and a conductive coating 66.
  • the conductive coating 66 is made up of an adhesion layer 68 and an external coating 70.
  • the electrode 60 can have a non-polymeric conductive body 62 such as steel or any other conductive material with the structured surface 64 and conductive coating 66.
  • the "structured surface” 64 is intended to describe any configuration of the body surface resulting from a structuring or texturing process as described herein.
  • the structured surface 64 can be made up of any known structures or morphology formed on the body that can result in an uneven or non-flat surface topography.
  • the structured surface 64 is made up of pillar-like structures.
  • FIG. 4 is a depiction of an actual structured surface of a polymeric body created by laser etching.
  • the structure surface 64 can be made up of other structures such as wrinkle-like structures or other types of mechanical features such as ridges, holes, voids, steps, etc.
  • the structured surface 64 is created by a laser etching process.
  • the process can be any laser etching process that uses UV wavelengths or picosecond pulses to ablate material. For example, a known dual beam interference procedure could be used.
  • any other known laser-based processes such as laser scanning or pulse techniques can be used.
  • the structure surface 64 can be created using any known printing process such as a hot stamp printing process.
  • the structured surface 64 is created using a known lithographic process.
  • the dimensions of the structures of the structured surface 64 can range from about 10 ⁇ m to about 100 ⁇ m. That is, the distances between the deepest points and the highest external points along the structured surface 64 vary within that range. Alternatively, the dimensions of the surface 64 can range from about 5 ⁇ m to about 50 ⁇ m. In a further alternative, the dimensions can range from about 20 ⁇ m to about 30 ⁇ m. [0030] As mentioned above, the conductive coating 66, according to one embodiment, coats, covers, or is otherwise disposed on the structured surface 64. As also mentioned above, the conductive coating 66 can be made up of two layers: an adhesion layer 68 and an external conductive coating 70.
  • the adhesion layer 68 is disposed between the structured surface 64 and the external conductive coating 70.
  • the adhesion layer 68 can be made up of titanium.
  • the adhesion layer 68 can be comprised of platinum, gold, silver, copper, tantalum, or niobium.
  • the adhesion layer 68 is made up of any similar known material that can serve as an adhesion layer between the structured surface 64 and the external coating 70.
  • the adhesion layer 68 can be applied to the structured surface 64 using any known sputtering or deposition process, according to one embodiment.
  • One such process is a chemical vapor deposition ("CVD") process.
  • the CVD process in accordance with one implementation, can coat the entire structured surface 64, including small crevices and gaps, with the adhesion layer 68.
  • the CVD process also can coat any connection lumen in communication with the conducting wire lumen (as described below) with the adhesion layer 68.
  • the adhesion layer 68 ranges from about 10 nm to about 1000 nm in thickness. Alternatively, the layer 68 ranges from about 10 nm to about 100 nm. In a further alternative, the layer 68 ranges from about 10 nm to about 30 nm.
  • the external coating 70 is disposed on or over the adhesion layer 68.
  • the adhesion layer 68 adheres the external coating 70 to the structured surface 64.
  • the external coating 70 can be made up of a ceramic such as iridium oxide, according to one embodiment.
  • the ceramic can be applied to the adhesion layer 68 according to a known application method.
  • iridium oxide is applied by a known physical vapor deposition process.
  • the iridium oxide can be applied by a known pulsed laser deposition process.
  • the iridium oxide can be applied by any other known method of applying iridium oxide.
  • the IROXTM structure and application methods according to one embodiment are described in some detail in U.S. Patents 4,679,572 & 4,762,136. [0037] Various processes can be used to achieve the various textured topographies discussed above.
  • the coating can be formed via an in-line flat target PVD system (physical vapor deposition using a rectangular chamber with a flat target).
  • a target material such as a ceramic (e.g. IROX) or a ceramic precursor metal (e.g. Ir).
  • the component to be coated is disposed within the chamber.
  • the cylinder also includes a gas, such as argon and oxygen. During the process, plasma formed in the chamber accelerates charged species toward the target, and target material is thereby sputtered from the target and deposited onto the stent.
  • the in-line flat target PVD system is suitable for application of the high frequency bias on the stent to realize the desired coating formation.
  • PVD arrangement is inversed cylindrical PVD system, which is described in U.S. Patent Application 11/752,772, which is hereby incorporated herein by reference in its entirety.
  • Another process that could be used herein is high frequency bias sputtering, which is described in Kim et al., Advances in Electronic Materials and Packaging, 2001 , EMAP 2001 , page 202-207, and further in U.S. Patent 4,897,172, both of which are hereby incorporated herein by reference in their entireties.
  • AC and DC sputtering are further exemplary processes that could be used herein.
  • SVC Society of Vacuum Coatings: C-103, An Introduction to Physical Vapor Deposition (PVD) Processes and C-248 - Sputter Deposition in Manufacturing, available from SVC 71 Pinion Hill, NE, Albequeque, NM 87122-6726, all of which are hereby incorporated herein by reference in their entireties.
  • a suitable cathode system is the Model 514, available from Isoflux, Inc., Rochester, NY.
  • Another sputtering technique that could be used herein includes closed loop cathode magnetron sputtering. Pulsed laser deposition could also be employed, and is described in U.S.
  • the resulting external coating 70 has a certain textured morphology or topography, according to one embodiment.
  • the surface is characterized by its visual appearance, its roughness, and/or the size and arrangement of the particular morphological features such as local maxima.
  • the textured topography of the external coating 70 is characterized by defined grains and high roughness.
  • the surface is characterized by definable sub-micron sized grains.
  • FIG. 5 provides one exemplary depiction of such a textured topography.
  • the defined grain, high roughness topography provides a high surface area characterized by crevices between and around spaced grains.
  • this particular topography is referred to as a "rice grain structure" because the grains resemble rice grains.
  • the grains have a length ranging from about 50 nm to about 500 nm. Alternatively, the grains have a length ranging from about 100 nm to about 300 nm.
  • the grains have a width ranging from about 5 nm to about 50 nm. Alternatively, they have a width ranging from about 10 nm to about 15 nm.
  • the grains have an aspect ratio (length to width) of about 5:1 or more. Alternatively, they have an aspect ratio of from about 10:1 to about 20:1.
  • the grains overlap in one or more layers. The separation between the grains can range from about 1 nm to about 50 nm.
  • these types of grains can resemble rice grains and thus the morphology can be referred to as a "rice grain structure.”
  • the textured topography of the external coating is characterized by a more continuous surface having a series of globular features separated by striations.
  • the striations have a width of about 10 nm or less.
  • the striations have a width of about 1 nm or less.
  • the striations have a width ranging from about 0.1 nm to about 1 nm.
  • the striations can be generally randomly oriented and intersecting.
  • the depth of the striations is about 10% or less of the thickness of the coating.
  • the depth of the striations ranges from about 0.1 to about 5% of the thickness of the coating.
  • the globular features separated by striations can resemble the surface of an orange peel.
  • the textured topography has characteristics ranging between high aspect ratio, definable grains and a more continuous globular surface.
  • the textured topography can include low aspect ratio lobes or thin planar flakes.
  • the operating parameters of the deposition system are selected to tune the morphology and/or composition of the ceramic.
  • the power applied during the process, total pressure, oxygen/argon ratio and sputter time are controlled.
  • the power applied during the process ranges from about 100 to about 700 watts.
  • the power ranges from about 100 to about 350 watts, from about 150 to about 300 watts, from about 340 to about 700 watts, or alternatively from about 400 to about 600 watts.
  • the total pressure ranges from about 1 to about 30 mTorr.
  • the total pressure can range from about 10 to about 30 mTorr, from about 1 to 10 mTorr, or alternatively from about 2 to about 6 mTorr.
  • the oxygen partial pressure ranges from about 10% to about 90%.
  • the oxygen partial pressure can range from about 80% to about 90%, such as for defined grain morphologies, or from about 10% to about 40%, such as for globular morphologies.
  • the deposition time can control the thickness of the ceramic and the stacking of morphological features. According to one embodiment, the deposition time can range from about 30 seconds to about 10 minutes. Alternatively, the deposition can range from about 1 to about 3 minutes. In one embodiment, the overall thickness of the ceramic ranges from about 50 nm to about 500 nm, or alternatively from about 100 nm to about 300 nm. It is understood that the oxygen content can be increased at higher power, higher total pressure, and high oxygen to oxygen ratios. [0046] Alternatively, the external coating 70 can be made up of various metals such as titanium, platinum, gold, tantalum, or any other similar metal.
  • the external coating 70 is made up of any conductive material that can produce the rice grain structure described above.
  • the metal for the external coating 70 can be sputtered onto the surface using a process called glancing angle deposition technique ("GLAD"). This process can provide defined peaks and valleys in the surface structure of the coating 70 to achieve a textured surface morphology as described above.
  • GLAD glancing angle deposition technique
  • the external coating 70 can be made up of a conductive polymer.
  • a conductive polymer is poly-ethylenedioxythiophene ("PEDT"), which is available from H. C. Starck, located in West Chester, OH. Two other examples include polyaniline- and polypyrrole.
  • PEDT poly-ethylenedioxythiophene
  • a conductive polymer could be applied by spray coating the polymer onto the surface from a solvent and then subsequently structuring or texturing the polymer using a laser.
  • the external coating 70 can be made up of a conductive metal such as platinum, gold, or iridium, or any other such conductive metal that can be used for such an external electrode coating.
  • the external coating 70 can have a thickness ranging from about 10 nm to about 100 nm.
  • the thickness of the coating 70 can range from about 100 nm to about 3,000 nm. In a further alternative, the thickness can range from about 100 nm to about 1 ,000 nm.
  • the combination of the structured surface 64 and the conductive coating 66 provides two levels of structure to the overall topology of the electrode 60: a larger or "coarser” base structure (the structured surface 64) and a smaller or “finer” outer structure. That is, the structured surface 64 provides a base topography in the micrometer range (varying in height by as much as 100 ⁇ m), while the outer topography of the conductive coating 66 is in the nanometer range (having a thickness of no more than 130 nm). [0051] Further, in accordance with one implementation, both levels of structure contribute to the hydrophobic and cell-repelling qualities of the electrode.
  • the combined topography of the structured surface 64 and the conductive coating 66 results in an overall topography that is hydrophobic, thereby resulting in a hydrophobic electrode.
  • the hydrophobic qualities cause the electrode to repel proteins and cells, thereby reducing the incidence of the electrode attaching to any tissue in the human body during use.
  • the hydrophobic qualities of the electrode surface are similar to the hydrophobic qualities of certain self- cleaning plants, because the hydrophobicity in both cases is caused by the overall surface topography.
  • a plant is the Lotus Flower, which exhibits extreme water-repellency or "superhydrophobicity" because of its topography, which is comprised of a hierarchical composition having both a "rough structure” and a "fine structure”.
  • the two levels of structure can also result in increased surface area, which makes it possible to deliver electrical current with lower impedance than would be possible with less surface area.
  • FIG. 6 depicts a cross-sectional view of an electrode 70, according to one embodiment.
  • the body 72 is a polymeric body 72 that has a lumen 74 in which the conductive wire (not shown) can be positioned.
  • the body 72 can also have a contact channel or lumen 76 in communication with the lumen 74 and the conductive coating 78 of the electrode 70.
  • the contact channel 76 provides electrical communication between the lead conductive wire disposed within the polymeric body and the conductive coating 78 of the electrode.
  • the polymeric body 72 is a core component of the lead body and is disposed throughout the length of the lead body.
  • the polymeric body 72 is a core component of solely the electrode, such that the electrode having the polymeric body 72 is coupled to the lead body.
  • a contact wire (not shown) can be disposed in the contact channel 76 and connected to the conductive coating 78 and the conductive wire to allow for electrical pulses to be transmitted to the electrode 70.
  • application of the adhesion layer for the conductive coating 78 as described above can result in the adhesion layer coating the inner wall of the contact channel 76, thereby providing the electrical communication between the coating 78 and the conductive wire disposed in the lumen 74.
  • the body 72 also has a second lumen 80.
  • the lumen 80 can house a second conducting wire or cable, e.g., in a multi-electrode lead.
  • the lumen 80 can be operable as a stylet or guidewire receiving lumen to facilitate lead delivery.
  • the lead body 72 can, in various other embodiments, include three or more lumens depending on the particular functionality desired.
  • Another embodiment relates to the method of making an electrode having a polymeric or non-polymeric conductive body with a structured surface and a conductive coating similar to the various electrode embodiments disclosed above.
  • the process includes forming a polymeric body having a lumen, structuring the surface of the polymeric body, adding an adhesion layer to the structured surface, adding a conductive external coating over the adhesion layer, and electrically coupling the external coating to a conductive wire disposed in the lumen of the polymeric body.
  • the process includes forming a metal body having a lumen, structuring the surface of the metal body, and electrically coupling the body to a conductive wire disposed in the lumen of the lead body.
  • the polymeric body can be formed by any suitable process, whether now known or later developed.
  • the process of forming a single or multi-lumen polymeric body includes extruding the lead body according to methods known in the art.
  • the structuring of the body surface and the addition or application of the adhesion layer and external coating can be accomplished by any of the methods disclosed above.
  • the electrical coupling of the conductive coating and conductive wire disposed in the lumen of the body can also be accomplished by any method discussed above.
  • the scope of the invention is not meant to be limited in application only to leads for implantation in coronary veins. Application of the disclosed embodiments may also be made to right sided bradycardia or tachycardia leads, or epicardial leads. For coronary venous applications, the disclosed embodiment may also be utilized on a non-electrode portion of the lead body.

Abstract

Les présents modes de réalisation concernent une électrode à revêtement comprenant une surface structurée et une couche conductrice et son procédé de fabrication. Les divers modes de réalisation d’électrode peuvent comprendre une topographie de surface qui minimise l’attachement aux tissus et facilite ainsi le retrait de l’électrode.
PCT/US2009/060219 2008-11-20 2009-10-09 Électrode repoussant les cellules comportant une surface structurée WO2010059305A1 (fr)

Priority Applications (3)

Application Number Priority Date Filing Date Title
EP09743985A EP2370150A1 (fr) 2008-11-20 2009-10-09 Électrode repoussant les cellules comportant une surface structurée
JP2011537451A JP2012509140A (ja) 2008-11-20 2009-10-09 構造化された表面を有する細胞反発性電極
AU2009317980A AU2009317980A1 (en) 2008-11-20 2009-10-09 Cell-repelling electrode having a structured surface

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US11658408P 2008-11-20 2008-11-20
US61/116,584 2008-11-20

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WO2010059305A1 true WO2010059305A1 (fr) 2010-05-27

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EP (1) EP2370150A1 (fr)
JP (1) JP2012509140A (fr)
AU (1) AU2009317980A1 (fr)
WO (1) WO2010059305A1 (fr)

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