WO2000047272A9

WO2000047272A9 - Cochlear electrode array with electrode contacts on medial side

Info

Publication number: WO2000047272A9
Application number: PCT/US1999/022591
Authority: WO
Inventors: Janusz A Kuzma
Original assignee: Advanced Bionics Corp
Priority date: 1999-02-09
Filing date: 1999-09-28
Publication date: 2001-07-19
Also published as: AU6404999A; CA2362478A1; WO2000047272A1; EP1159027A4; US6129753A; US6144883A; CA2362478C; EP1159027A1; EP1159027B1

Abstract

An implantable electrode array (30), adapted for insertion into a human cochlea, provides improved stability of electrode contact direction. In-line electrodes (32) are spaced-apart along one side of a flexible carrier. The structure of the electrode array facilitates bending of the array with the electrode contacts on the inside of the bend, yet deters flexing or twisting of the array in other directions. The electrode contacts preferably are each made from two strips of metal (210, 220), arranged in a 'T' shape (top view). During assembly, all of the 'T' strips are held in position on an iron sheet (100). Two wire bundles (202, 203) are formed that pass along each side of each 'T'. The leg of each 'T' is folded over to pinch at least one of the wires from one of the wire bundles therebetween. This pinched wire is then resistance welded to the strip. The sides of the 'T' are then folded up. In one embodiment, the sides touch or nearly touch to form a 'Δ' shape (FIG. 5A). In another embodiment, the sides are directed upwards to form a 'U' shape (FIG. 6B). The wire bundles going to more distal electrodes pass through The 'Δ' or 'U' and are engaged thereby. A flexible carrier (36), made from, e.g., silicone rubber, is molded over and around the wire bundles and folded electrode T's, preferably in a slightly curved shape. The iron sheet is chemically etched away, leaving an array of spaced-apart electrode contact areas along one edge of the flexible carrier, each of which is electrically attached to at least one wire which passes through the carrier. In one embodiment, soft shoulders (70) or bumps or ridges are formed in between each electrode contact. A soft tip (37), which in some embodiments may be enlarged into a ball (37'), and which is made from a material that is softer than the flexible carrier, is formed at a distal end of the flexible carrier (36).

Description

COCHLEAR ELECTRODE ARRAY WITH ELECTRODE CONTACTS ON MEDIAL SIDE

Background of the Invention The present invention relates to implantable stimulation devices, e.g , cochlear prosthesis used to electrically stimulate the auditory nerve, and more particularly to an electrode array for use with a cochlear stimulator that is designed to place the electrode contacts of the electrode array generally along one side of the array so that when the array is implanted within the cochlea, or other body cavity, the side of the array whereon the electrode contacts are located can be positioned in close proximity to the cells that are to be simulated, thereby allowing such cells to be stimulated with minimal power consumption. For example, where the array is implanted into the cochlea, the electrode side of the array may be positioned closest to the modiolar wall, thereby placing all of the individual electrode contacts in close proximity to the ganglion cells and thereby m close proximity to the auditory nerve fibers. Heaπng loss, which may be due to many different causes, is generally of two types: conductive and sensoπneural. Of these, conductive heaπng loss occurs where the normal mechanical pathways for sound to reach the hair cells in the cochlea are impeded, for example, by damage to the ossicles. Conductive heaπng loss may often be helped by use of conventional heaπng aids, which amplify sound so that acoustic information does reach the cochlea and the hair cells. Some types of conductive heaπng loss are also amenable to alleviation by surgical procedures.

In many people who are profoundly deaf, however, the reason for their deafness is sensoπneural heaπng loss. This type of heaπng loss is due to the absence or the destruction of the hair cells m the cochlea which are needed to transduce acoustic signals into auditory nerve impulses. These people are unable to deπve any benefit from conventional heaπng aid systems, no matter how loud the acoustic stimulus is made, because their mechanisms for transducing sound energy into auditory nerve impulses have been damaged. Thus, in the absence of properly functioning hair cells, there is no way auditory nerve impulses can be generated directly from sounds. To overcome sensoπneural deafness, there have been developed numerous cochlear implant systems —or cochlear prosthesis- which seek to bypass the hair cells 'n the cochlea (the hair cells are located in the vicinity of the radially outer wall of the cochlea) by presenting electπcal stimulation to the auditory nerve fibers directly, leading to the perception of sound in the brain and at least partial restoration of heaπng function. The common denominator in most of these cochlear prosthesis systems has been the implantation into the cochlea of electrodes which are responsive to a suitable external source of electπcal stimuli and which are intended to transmit those stimuli to the ganglion cells and thereby to the auditory nerve fibers.

A cochlear prosthesis operates by direct electrical stimulation of the auditory nerve cells, bypassing the defective cochlear hair cells that normally transduce acoustic energy into electrical activity in such nerve cells. In addition to stimulating the nerve cells, the electronic circuitry and the electrode aπay of the cochlear prosthesis performs the function of the separating the acoustic signal into a number of parallel channels of information, each representing the intensity of a narrow band of frequencies within the acoustic spectrum. Ideally, each channel of information would be conveyed selectively to the subset of auditory nerve cells that normally transmitted information about that frequency band to the brain. Those nerve cells are arranged in an orderly tonotopic sequence, from high frequencies at the basal end of the cochlear spiral to progressively lower frequencies towards the apex. In practice, this goal tends to be difficult to realize because of the anatomy of the cochlea.

Over the past several years, a consensus has generally emerged that the scala tympani, one of the three parallel ducts that, in parallel, make up the spiral-shaped cochlea, provides the best location for implantation of an electrode array used with a cochlear prosthesis. The electrode array to be implanted in this site typically consists of a thin, elongated, flexible carrier containing several longitudinally disposed and separately connected stimulating electrode contacts, perhaps 6-30 in number. Such electrode array is pushed into the scala tympani duct to a depth of about 20-30 mm via a surgical opening made in the round window at the basal end of the duct. During use, electrical current is passed into the fluids and tissues immediately surrounding the individual electrode contacts in order to create transient potential gradients that, if sufficiently strong, cause the nearby auditory nerve fibers to generate action potentials. The auditory nerve fibers arise from cell bodies located in the spiral ganglion, which lies in the bone, or modiolus, adjacent to the scala tympani on the inside wall of its spiral course. Because the density of electrical current flowing through volume conductors such as tissues and fluids tends to be highest near the electrode contact that is the source of such cuπent, stimulation at one contact site tends to activate selectively those spiral ganglion cells and their auditory nerve fibers that are closest to that contact site. Thus, there is a need for the electrode contacts to be positioned as close to the ganglion cells as possible. This means, in practice, that the electrode array, after implant, should preferably hug the modiolar wall, and that the individual electrodes of the electrode array should be positioned on or near that surface of the electrode array which is closest to the modiolar wall.

In order to address the above need, it is known in the art to make an intracochlear electrode array that includes a spiral-shaped resilient carrier which generally has a natural spiral shape so that it better conforms to the shape of the scala tympani. See, e.g., United States Patent No.4,819,647. Unfortunately, while the electrode array with spiral-shaped earner shown in the '647 patent represents a significant advance m the art, there exists lack of sufficient shape memory associated with the earner to allow it to return to its oπgmal curvature (once having been straightened for initial insertion) with sufficient hugging force to allow it to wrap snugly against the modiolus of the cochlea.

It is also known in the art, as shown in applicant's pnor patents, U.S. Patent Nos. 5,545,219 and 5,645,585, to construct an electrode earner from two initially straight members, a rod-like electrode earner and a flexible rod-like positioning member. As shown in these patents, the two members extend m substantially parallel relation to and closely alongside each other, but are connected to each other only at their respective leading and trailing end regions. After implant, a pushing force is applied to the positioning member so that it is forced to assume an outwardly arched configuration relative to the electrode earner, thereby forcing the electrode earner into a close hugging engagement with the modiolus, thereby placing the electrode contacts of the electrodes in as close a juxtaposition to the cells of the spiral ganglion as possible. The '219 patent, in particular, provides m FIGS. 1-10 and accompanying text an excellent summary of pnor art electrodes and the deficiencies associated therewith.

Unfortunately, while the electrode array taught m the above-referenced '219 and '585 patents has the nght idea, i.e., to force the electrode earner into a close hugging engagement with the modiolus, it does so only by use of an additional element that makes manufacture of the lead more difficult and expensive, and only through application of an additional pushing force which is applied to an electrode structure after it is already fully inserted into the cochlea. Such additional pushing force may easily cause damage to the delicate scala tympani. Moreover, the entire electrode array may twist dunng the insertion process, or when the additional pushing force is applied, thereby causing the electrode contacts to twist and/or be forced away from the modiolus, rather than in a hugging relationship therewith.

Thus, while it has long been known that an enhanced performance of a cochlear implant can be achieved by proper placement of the electrode contacts close to the modiolar wall of the cochlea, two mam problems have faced designers m attempting to achieve this goal. First, it is extremely difficult to assemble electrode contacts on the medial side of the an electrode array, facing the modiolus of the cochlea. Second, heretofore there has either been the need for application of an external (and perhaps unsafe) force, or a lack of sufficient shape memory, to allow the electrode (after initial straightening to facilitate insertion) to assume or return to the desired curvature needed to place the electrodes against the modiolar wall so that the curvature wraps snugly around the modiolus of the cochlea As a result, the electrode contacts of the pnor art electrodes are generally positioned too far way from the modiolar wall.

Many cochlear electrode arrays of the pnor art are made for insertion into a left cochlea, or a nght cochlea, depending upon the oπentation of the electrode contacts one to another. It would be desirable for a universal electrode array to be made that could be used in either cochlea, left or nght, without concern for whether the electrodes were onentated m a nght or left side onentation.

It is thus evident that improvements are still needed in cochlear electrodes, particularly to facilitate assembling an electrode so that the electrode contacts are on the medial side of the electrode array, and to better assure that the electrode assumes a close hugging relationship with the modiolus once implantation of the electrode has occurred.

Further, applicant has previously invented, as shown in applicant's pnor publication, W099/11321, published 11 March 1999, Senal No. PCT/US98/17784. an electrode system that includes both a flexible electrode and a separate, detached, positioner element. While the positioner element shown in the referenced PCT document may be used with any type of flexible electrode, such positioner element is most effective when used with an electrode having its electrode contacts along one side —a medial side— of the electrode, and wherein the medial side of the electrode is intended to be placed proximate the modiolar wall within the cochlea. The present invention advantageously discloses the details associated with making and using such a preferred universal electrode.

Summary of the Invention

The present invention addresses the above and other needs by providing a universal electrode array, adapted for insertion into either a left or nght cochlea, which provides improved stability of electrode contact direction. All of the electrode contacts are spaced apart along one edge or side of the aπay, termed the "medial side". Advantageously, the structure of the electrode array facilitates bending of the array with the electrode contacts on the inside of the bend, yet deters flexing or twisting of the aπay that would tend to position or point the electrode contacts away from the mside of the bend. Hence, when inserted into the scala tympani duct of a cochlea, all of the electrode contacts on the medial side of the array face the modiolus of the cochlea.

In the prefeπed embodiment, the electrode contacts of the aπay each compnse two stπps of metal, arranged m a "T" shape (as viewed from a top view of the strips). Duπng assembly, all of the "T" stπps are held m a spaced apart, in-line, position on an iron sheet. Two wire bundles are formed that pass along each side of each "T" The leg of each "T" is folded over to pmch at least one of the wires from one of the wire bundles therebetween, which wire is then resistance welded to the stπp. The sides of the "T" are then folded up and touch or nearly touch to form a "Δ" shape (as viewed from a side view of the stnps). The wire bundles gomg to other electrodes of the aπay pass through the "Δ" Sihcone rubber, or a similar substance, is molded over and around the wire bundles and folded electrode T's, to form the earner. Preferably, the earner is molded in a slightly curved shape in the region where the electrode contacts are located, The iron sheet is chemically etched away, leaving an aπay of spaced-apart electrode contacts along one edge of the flexible earner, each having an exposed surface area that is typically flat with a rectangular shape. Each electrode contact area is electπcally attached to at least one of the wires which passes through the earner.

Advantageously, the electrode aπay of the present mvention can be manufactured using easy, low cost technology; and once made can be easily inserted, removed and reinserted, if required, into the cochlea or other curved body cavity.

In one embodiment, small non-conductive bumps or humps are formed in the earner between the electrode contact areas on the medial side of the aπay. These small bumps are made, e.g., from a soft sihcone rubber, or equivalent substance. When inserted into the cochlea, the small bumps serve as non-irπtatmg stand-offs, or spacers, that keep the electrode contacts near the modiolus wall, but prevent the electrode contacts from actually touching the modiolus wall. The bumps may also serve as dielectnc insulators that help steer the stimulating electncal cuπent in the desired direction, towards the modiolus.

Once the electrode aπay of the present invention, with its electrode contacts all facing the modiolus, has been inserted into the cochlea, a flexible positioner may be inserted behind the electrode aπay so as to force the electrode contacts up against the modiolar wall. The descnption and use of such a positioner is not the subject of the present application, but is described in Applicant's previously-referenced PCT application, PCT/US98/17784. However, it is to be understood that although the positioner descnbed in the subject PCT patent applications may be used with the electrode aπay of the present invention, the electrode aπay herein described is not limited to use with such a positioner. Rather, because the electrode aπay descnbed herein will most often have its electrode contacts facing in the medial direction without concern for twisting of the earner (and hence without concern for having the electrode contacts pointing away from the medial direction), it offers advantages not heretofore available with prior art electrode aπays.

Insertion of the electrode aπay into the cochlea may be performed in conventional manner, e.g., using the electrode insertion tool described in United States Patent Number 5,443,493. Equivalent or similar insertion tools may also be used, such as that shown in Applicant's co-pending U S. patent application, Seπal No. 09/313,901, filed 18 May 1999.

Advantageously, the electrode aπay of the present invention achieves the following goals: (1) it helps assure that the electrode contacts of the electrode aπay will be optimally positioned facing the medial direction, e.g., facing the modiolar wall in a cochlea of any size or any side (left or nght) of the body; (2) it flexes or bends more readily m the medial direction than in a lateral direction, thereby helping to assure that it will not twist and thereby face the electrode contacts away from the modiolar wall dunng the insertion process, and thereafter; (3) it better focuses or directs electncal stimulation cuπent from each exposed electrode contact to the modiolar wall; (4) it can be manufactured using easy, low cost technology; and (5) it can be easily inserted into the cochlea, and removed and reinserted, if required.

Bnef Descnption of the Drawings

The above and other features and advantages of the present invention will be more apparent from the following more particular descnption thereof, presented in conjunction with the following drawings wherem:

FIG. 1 depicts an electrode aπay and associated lead for attachment to an implantable cochlear stimulator in accordance with the present invention;

FIG. 2 illustrates a side view of the proximal end of the lead of FIG. 1; FIG 3 is a more detailed view of the offset portion of the lead/aπay of FIG. 1;

FIG. 3 A is a sectional view taken along the line 3A-3A of FIG. 3;

FIG. 4 shows the electrode aπay of the present invention having spaced-apart electrode aπay contacts along the medial side of the aπay, which electrode aπay compnses the distal end of the lead/aπay of FIG. 1; FIG. 5 shows a detail view of the electrode aπay contacts of the electrode aπay of FIG. 4;

FIG. 5 A is a sectional view of the electrode aπay taken along the line 5 A-5 A of FIG. 5;

FIG. 6 shows an alternative embodiment of the electrode aπay of the present invention wherein bumps are formed in the space between each electrode contact;

FIG. 6A shows a detail view of the electrode aπay contacts of the alternative electrode aπay of FIG. 6;

FIG.6B is a sectional view of the alternative electrode aπay taken along the line FIG. 7A depicts a prefeπed manner of making a multi-electrode contact aπay in accordance with the present invention,

FIG. 7B shows an enlarged view the "T" stπps used in making the electrode contacts of the aπay of FIG. 7A, FIGS. 8A, 8B, 8C and 8D illustrate one manner m which wires are bonded and routed to each of the "T" stnp electrode contacts of FIG. 7B dunng manufacture of the electrode aπay;

FIG. 9 depicts a molding die onto which the partially- formed electrode aπay of FIG. 7 A, with wires attached to each of the electrodes as shown in FIGS. 8A-8D, may be mounted in order to form a straight polymer earner for the electrode aπay; and

FIGS. 10 and 11 illustrate a perspective and side exploded view, respectively, of an alternative type of molding die onto which the partially-formed electrode aπay of FIG.7A, with wires attached to each of the electrodes as shown in FIGS. 8A-8D, may be mounted in order to form a curved polymer earner for the electrode aπay. Coπespondmg reference characters indicate coπespondmg components throughout the several views of the drawings.

Detailed Descnption of the Invention

The following descnption is of the best mode presently contemplated for carrying out the invention. This descnption is not to be taken m a limiting sense, but is made merely for the purpose of descnbmg the general pnnciples of the invention. The scope of the invention should be determined with reference to the claims.

The invention descnbed herein teaches a particular type of implantable electrode aπay having multiple, in-line, electrode contacts. Here, the term "in-line", used to descπbe the electrode contacts, means only that the electrode contacts are spaced apart more or less in alignment with the longitudinal axis of a lead. It does not mean that a perfect, straight alignment with the lead axis must be achieved. For example, electrode contacts that zig-zag somewhat with respect to the lead axis would still be considered to be "m-lme" electrodes for purposes of the present invention. Thus, in general, "in-line" means that of two adjacent electrode contacts, one will be more distal than the other. Further, all of the in-line electrode contacts will have an exposed surface which, more or less, lies on the same side —the medial side— of the curved electrode.

The electrode aπay of the present invention may be best used with an implantable multichannel pulse generator, e.g., an implantable cochlear stimulator (ICS) of the type disclosed in United States Patent No 5,603,726. or other suitable stimulator. It is to be understood, however, that although a cochlear electrode aπay is hereafter descnbed, having dimensions suitable for insertion into the cochlea, the pnnciples of the invention may be applied to other types of implantable leads for applications other than cochlear stimulation.

The electrode aπay of the present invention is particularly adapted to bend or flex m one direction, thereby making it suitable for insertion into a curved body cavity, such as the scala tympani of the cochlea.

An important feature of the electrode aπay of the present invention is that all of the active electrode contacts of the aπay are generally positioned along one side, e.g., the medial side (the inside of the curve or bend), of the aπay. Thus, when inserted into the curved or spiralmg cochlea, which may advantageously be either a left or nght cochlea, wherein the cells to be stimulated are located with the center modiolar wall, the electrode contacts are positioned proximate the modiolus, where they are closest to the cells to be stimulated. (The "modiolus" is the conical central pillar of the cochlea where the spiral ganglion cells are located.) Hence, the electrode aπay of the present invention facilitates stimulation of the desired cells at lower power levels than would otherwise be needed if the electrode contacts were not proximate the modiolar wall.

Another feature of the electrode aπay of the present invention is that the electrode contacts have, in the prefeπed embodiment, a relatively large exposed electrode surface area that is generally planar or flat having a desired geometnc shape, e.g., rectangular, semicircular, or oval. However, it is to be understood that the pnnciples of the invention may also be practiced with electrodes that have exposed surface areas that are not flat, e.g., dimpled, or corrugated, or pitted, and that may have an exposed surface area that has lπegular geometnc shapes.

Except as noted herein, the matenals from which the electrode aπay of the mvention is made, and the manner of making the electrode aπay, may be conventional, as are known m the art.

A prefeπed electrode aπay 30 in accordance with the present invention is shown in FIG. 1. The electrode aπay 30 forms the distal end of a lead/aπay assembly 40 adapted to be connected to an implantable cochlear stimulator (ICS), not shown. The lead/aπay assembly 40 includes the electrode aπay 30, a fantail proximal connector 42, and a lead body 44 connecting the aπay 30 to the proximal connector 42. The ICS is typically housed withm a ceramic or other case, such as is disclosed in United States Patent No. 4,991,152. The case has an aπay of feedthrough terminals coπesponding to its multiple channels. A prefeπed ICS has eight channels, with each channel having two feedthrough terminals connected thereto. Such terminals are typically labeled as Ml and LI (for medial and lateral) for the first channel, M2 and L2 for the second channel, and so on, up to and including M8 and L8 for the eighth channel. The feedthrough terminals are spaced across a header of the case. Inside the case, each feedthrough terminal is connected to appropnate electronic circuitry for the coπesponding channel, as taught m the previously-referenced '726 patent. On the outside of the case, each feedthrough terminal is connected to a coπesponding wire conductor within the lead/aπay assembly 40. Such wire conductors are identified in FIG. 1 by the numbers 1 through 16. The wire conductors 1 - 16 are of necessity spread out at the point where they connect to the feedthrough terminals of the header. Thus, the proximal end of the lead/assembly 40 includes the fantail connector 42 that funnels the spread conductors 1 - 16 at the point they connect to the feedthrough terminals down to the lead body 44 A side view of the fantail connector 42 is shown in FIG. 2.

The manner of forming the fantail connector 42, and connecting it to the feedthrough terminals may be conventual, and does not form part of the present invention. Rather, the present invention is directed to the electrode aπay 30 at the distal end of the lead/assembly 40 It should be emphasized that the electrode aπay 30 is not limited to use with a proximal fantail connector 42 and the type of ICS disclosed m the '726 patent. Rather, the electrode aπay 30 may be used with any type of proximal connector that interfaces with an appropnate pulse generator. As seen m FIG. 1, the electrode aπay 30 is preferably curved an appropnate amount. A multiplicity of in-line electrode contacts 32 are spaced apart so as to e on the medial side (mside of the curve) of the aπay. Sixteen such electrode contacts 32 are used in a prefeπed embodiment of the aπay 30. These electrode contacts are respectively connected to the wire conductors 1-16 withm the lead. As shown in FIG. 1, the most distal electrode contact is connected to wire conductor 1 withm the lead 44, which in turn is connected to the feedthrough terminal LI at the pulse generator The second-most distal electrode contact is connected to wire conductor 2 within the lead 44, and is connected to the feedthrough terminal Ml at the pulse generator. In this manner, the two-most distal electrode connectors 32 on the aπay may be connected to the first channel of the implantable pulse generator. In a similar manner, the two most proximal electrode contacts on the aπay 30 are connected to wire conductors 15 and 16 within the lead 44, and are connected to feedthrough terminals L8 and M8, coπespondmg to the eighth channel, of the implantable pulse generator. The other electrode contacts 32 included within the aπay 30 are similarly connected to a coπesponding channel withm the pulse generator. As further seen in FIG 1, the electrode aπay 30 may also include three reference electrode contacts 34, identified m FIG. 1 by the electrode numbers 17, 18 and 19. Such reference contacts 34 are not connected to any wire conductors within the lead 44, and for this reason are sometimes refeπed to as "dummy reference contacts". Each of these reference contacts 34 may provide a reference indicator or marker to the physician inserting the electrode aπay relative to the depth of insertion

As also seen in FIG. 1 , the lead/aπay assembly 40 further includes an offset portion 46 that effectively marks the end of the lead 44 and the beginning of the electrode aπay 46. Such offset portion 46 facilitates insertion of the electrode aπay 30 into the scala tympani duct of the cochlea. The insertion process may be conventional, and is aided by a special tool of the type disclosed m the '493 patent, previously referenced, or an equivalent tool.

Turning next to FIG 3 , there is shown a more detailed view of the offset portion 46 of the lead/aπay 40. A sectional view of the offset portion 46, taken along the line 3A-3A of FIG.3, is shown in FIG. 3 A. As seen in these figures, the offset portion 46 separates the body of the lead 44 from the body of the aπay 30 by an offset distance L4. When measured from a center-line longitudinal axis 45 of the lead 44 to a center-line longitudinal axis 35 of the array 30, this distance L4, in the prefeπed embodiment, is about 1.3mm. At the point of the offset, the diameter of the lead 44 is a distance L5, while the diameter of the electrode aπay is a distance L6. In the prefeπed embodiment, both L5 and L6 are about 0.8mm. The length L9 of the offset portion 46 is approximately 1.6mm, allowing the wire conductors 1-16 withm the electrode aπay 30 to transition to the lead body 44 without too sharp of a bend. It is to be understood that these dimensions, as well as other dimensions presented herein, are only exemplary of one embodiment, and are not meant to be limiting.

Typically, as seen in FIG. 3, the body of the lead 44 may be made from a sihcone rubber tube 43 that is inserted into the proximal end of the electrode aπay 30 up to a specified distance L 12 from the first active electrode contact 16 In the prefeπed embodiment, L12 is approximately 3.0mm, and the outer diameter of the tube 43 is approximately 0.64mm. What this means, as a practical manner, as will become evident from the descnption below, is that the distal end of the tube 43 is positioned a distance L12 from the electrode contact 16 when the electrode aπay 30 and offset portion 46 are formed through a molding process.

The matenal from which the lead/aπay 40, including the electrode aπay 30, is made may be any suitable biocompatible matenal commonly used with implantable leads and other implantable components as is known in the art. A suitable material, for example, is a type of sihcone polymer (sometimes refeπed to as "Silastic") or rubber known as LSR-70 or LSR-25. The properties of LSR-70 and LSR-25 are well known in the art, and LSR-70 and LSR-25 may be obtained commercially from numerous sources, LSR-70 is formed into a desired shape by injecting or otherwise inserting it into a mold while in a liquid state and allowing it to cure m the mold at a specified temperature for a specified time penod. For example, LSR-70 may cure at a temperature of 140 degrees C for about 15 minutes. LSR-25 may likewise be formed into a desired shape using a similar molding process, or it may be applied through a suitable applicator, e.g, a syπnge, to a desired area and then formed into a desired shape. LSR-25 is essentially the same as LSR-70 except that when it cures it is significantly softer, i.e., more pliable. Both LSR-70 and LSR-25 readily adhere to the tubing so that when cured they become integral therewith Hence, as explained more fully below, m some embodiments of the invention, a suitable length of tubing 43 may be used to form a central core of the lead, thereby providing a lumen or hole through the center of the lead into which a wire stylet may be inserted to help insert the lead into the cochlea, or that may be used for other purposes.

Still with reference to FIG. 3, it is seen that the distance from the proximal end of the electrode aπay 30 to the proximal edge of electrode contact 16 (i.e., the electrode contact 32 that is connected to wire conductor 16) is a distance L3. In the prefeπed embodiment, the distance L3 is about 10.5mm.

Next, with reference to FIG 4, a more detailed view of the electrode aπay 30 is shown. The electrode aπay includes electrode aπay contacts 32 equally-spaced along a medial side of a flexible earner 36. The flexible earner 36 is made from LSR-70, and is molded around an assembly of electrode contacts 32 and interconnecting wires as descnbed below m conjunction with FIGS. 7A-11. The elecfrode aπay 30 has an overall length L7. Such length L7 is most easily measured when the aπay 30 is straightened, as shown by the dotted lines in FIG. 3. In the prefeπed embodiment, L7 has a value of approximately 25mm. While the electrode aπay 30 could be formed to assume any desired shape, in the prefeπed embodiment it is formed to include a natural curve having a radius of curvature r2, with the electrode contacts 32 being positioned along the inside of the curve. The radius of curative r2 may have a value of approximately 9.0mm.

As further seen in FIG. 4, a soft tip 37, having a depth of distance L8, is typically formed from LSR-25 at the very distal tip of the electrode aπay 30. In the prefeπed embodiment, L8 has a value of approximately 0 3mm. In some embodiments of the electrode, this soft tip 37 may be enlarged to assume the shape of a ball 37' (phantom lines) at the distal tip. Such soft-ball tip functions as a soft bumper and facilitates insertion of the electrode, and m particular minimizes any trauma or damage that the tip might otherwise cause to the basilar membrane (or other delicate surfaces) inside of the cochlea. As additionally illustrated in FIG.4, the reference marker contacts 34, identified as electrodes 17, 18 and 19, are spaced from the active electrode 16 a distance LI 1, with a spacing between the reference marker electrodes of L10. In the prefeπed embodiment, the distance LI 1 is about 3.0mm, and the distance L10 is about 1.0mm. Refernng next to FIG. 5, a prefeπed spacing between the individual electrode contacts 32 is depicted. Such spacing, as well as all the other dimensional detail presented herein, is exemplary of a cochlear electrode, and is not intended to be limiting. As seen m FIG. 5, each exposed electrode contact surface area compnses a generally rectangular-shaped area having a length LI and a width Wl . Other shapes could also be used. In the prefeπed embodiment, the rectangular area is roughly a square, with LI and Wl each having a value of approximately 0.4mm ±10%, thereby providing an exposed electrode surface area of approximately 0.16 mm² The spacing between coπesponding points of adjacent electrode contact areas 32 is a distance L2. L2 has a nominal value of approximately 0.9mm ± 0.1mm.

The electrode contact areas compnse an exposed surface of an electrode contact 32 that is formed from folded stnps 210 and 220 of a biocompatible metal, such as platinum, as descnbed more fully below in conjunction with FIGS. 7A-8D. Such electrode contacts are embedded within the molded earner 36 as illustrated in the sectional view of FIG. 5A, which is taken along the lines 5A-5A of FIG. 5. As seen m FIG. 5 A, the earner 36 is formed to have a cross-sectional area that is generally rectangular, having dimensions of X by Y mm, where the values of X and Y vary as a function of where along the length of the earner the cross section is viewed. At elecfrode 16 (near the proximal end of the electrode/aπay 30), for example, X and Y are both about 0.8mm. At electrode 1 (near the distal tip of the elecfrode aπay), X and Y are both about 0.6mm. Thus, it is seen that the earner 36 is tapered along its length so that it has a smaller cross section at its distal tip than it does at its proximal end. Still with reference to the cross-sectional view of the aπay shown m FIG. 5 A, it is seen that the sectional shape has rounded corners on the side opposite the medial side. (As explained previously, the medial side is the side where the electrode contacts 32 are located.) The rounded corners have a radius of curvature r 1 that is approximately 0.3mm in the prefeπed embodiment. The electrode contacts 32 have a general cross sectional shape, as seen m FIG.

5A, and as will be more evident from the descnption below of FIGS. 7A-8D below, that resembles a triangle. The base of this tnangular-shaped (or "Δ-shaped") electrode forms the exposed electrode contact area along the medial side of the electrode aπay, e.g., as seen m FIG. 5. The upward sloping legs 220 of this Δ-shape electrode extend into the body of the earner, e.g., as anchors, and thus become embedded (non-exposed) portions of the electrodes. It should be noted that while in the prefeπed embodiment the upward sloping legs 220 touch at their respective tips to form the Δ shape, such touching is not required; nor is the Δ shape required. What is important is that these legs 220 extend into the body of the earner, m some fashion, so that the electrode is firmly anchored in its desired position along the length of the aπay. For example, m some embodiments, the legs 220 may be completely folded over so as to he almost flat on top of the exposed surface area, as shown generally applicants PCT application, PCT/US98/ 17784 (W099/ 11321). In other embodiments, the legs 220 may extend more or less straight into the body of the earner, forming a generally block "U" cross-sectional shape, thereby facilitating the use of a silastic tube 43 as a core of the electrode aπay, as shown below in FIG. 6B.

Wire bundles 202 and 203 pass through the corners of the Δ-shaped (or U- shaped or other-shaped) electrodes and become embedded within the molded earner 36 when formed. As explained in more detail below, at least one wire from at least one of these wire bundles makes electrical contact with each active electrode. The wires that do not make elecfrical contact with an electrode contact are nonetheless engaged by or supported by the embedded portion of the electrode as they pass through the Δ (or U or other) shape. Such engagement helps support and position the wire bundles pnor to molding the earner over them. Moreover, the location of the wire bundles immediately behind and along opposing edges of the exposed surface area of the electrodes helps add additional stiffness to the electrode aπay, once formed, m the lateral direction, as explained below, thereby making it more difficult to bend or twist the aπay m the lateral direction. In contrast, the aπay remains relatively easy to bend in the medial direction. As used herein, the medial direction is the direction of curvature defined by the radius r2 (FIGS 4 and 6)

An alternative embodiment an electrode aπay 30' made in accordance with the present mvention is shown m FIGS. 6, 6A and 6B. This alternative electrode aπay 30' is the same as the aπay 30 illustrated in FIGS. 4, 5 and 5A with the exception that a senes of small non-conductive bumps, or humps 70, are formed between the electrode contact areas 32. As seen best in FIG. 6B, these humps 70 have a height HI of about 0.13 mm, and as seen best m FIG. 6A, have a width W2 of about 0.25mm As further seen best in FIG. 6, the humps 70 extend out from the medial surface of the electrode aπay. The humps 70 are made from a soft sihcone rubber, or equivalent substance, such as LSR-25. When inserted into the cochlea, the small bumps 70 serve as non-irntatmg stand-offs, or spacers, that allow the electrode contacts 32 to be positioned near the modiolus wall, but prevent the electrode contacts 32 from actually touching the modiolus wall. The humps 70 further serve as dielectnc insulators that help steer the stimulating electπcal cuπent, flowing to or from the electrode contacts, in the desired direction, from or towards the cells located in the modiolar wall. The embodiment of the electrode aπay shown in FIGS. 6, 6A and 6B further shows the use of a silastic tube 43 that may be optionally used to form the core of the flexible earner 36 Except for the presence of the humps 70, and the tubing 43, FIGS. 6, 6A and 6B coπespond to FIGS. 4, 5 and 5A. One of the advantages of the present invention is that the electrode aπay is easy and relatively inexpensive to manufacture. A prefeπed method of making the electrode aπay 30 or 30' is illustrated, for example, in FIGS. 7A through 11. It is to be emphasized that the method depicted in these figures of making the electrode aπay is not the only way an electrode aπay 30 or 30' could be made. However, it represents an easy and inexpensive (and thus a prefeπed) way to make the electrode aπay.

Most designs of electrodes and connectors are based on the pnnciple of molding a contact or aπay of contacts, usually made from biocompatible metal, into a polymer earner like sihcone or polyurethane rubber. The electrode contacts are usually required to be located in a controlled position in reference to the surface of the earner, with specified surface areas to be fully exposed to the stimulated or interconnection area. Disadvantageously, making such electrodes or connectors becomes extremely difficult, especially when the contacts are very small and/or a large number of contacts are required, e.g., as is the case with a cochlea electrode. One of the mam problems encountered m the fabncation of such electrodes or connectors is to find a reliable method of holding the system of contacts in the desired and stable position duπng the process of welding the connecting wires and molding the polymer earner. A further problem relates to maintaining a controlled surface of the contacts that are to remain exposed, i.e., to ensure that the contacts are not covered by the polymer when the earner is molded.

The prefeπed methods of making the elecfrode aπay 30 or 30' descnbed below m connection with FIGS. 7 A through FIG. 11 are based on the pnnciple of attaching (by the process of resistance welding) electrode contacts made from precious, biocompatible matenal (such as platinum or its alloys) to a foil earner made from a non-toxic but chemically-active metal, such as iron (Fe). Resistance welding advantageously provides a secure attachment of the electrode matenal to the foil earner without causing a deep fusion of the two mateπals being attached. The resulting shallow fusion contact, in turn, allows clean exposed electrode surface areas to be formed when the foil earner is eventually chemically etched away, as explained below. Other types of attachment that result m shallow fusion of the electrode matenal and the foil earner sheet material may also be used in lieu of resistance welding.

Attached to the metal earner, the electrode contacts remain in a desired and stable position allowing easy connecting of the wmng system and subsequent molding of the polymer earner After completion of the molding process, the metal foil earner is chemically etched away using a mixture of diluted acids, such as HN0₃ and HC1. The precious metal contacts and polymer are immune to the acid and remain in their mtact, unaltered shape, and thereby provide the desired elecfrode aπay structure

To illustrate the method, the method will be descnbed relative to the fabncation of the elecfrode aπay 30 or 30' suitable for insertion into the cochlea. As a first step, an aπay of contacts 200 are resistance welded onto an iron earner 100 so as to assume a desired in-line spaced-apart relationship, as shown in FIG. 7A. Each contact 200 consists of two pieces of platinum foil 210 and 220, connected together and joined to the earner 100 by a shallow-fusion spot weld 230, as shown in FIG. 7B. The width of the stnp 210 is approximately Wl, and the width of the stnp 220 is approximately LI . These stnps are aπanged to form a "T" shape, when viewed from a top view, with the stnp 210 forming the leg of the "T", and with the stnp 220 forming the cross bar of the "T". Moreover, the legs of each "T", are aπanged in-line, with the proper spacing L2 therebetween, as shown in FIG. 7A.

As a second step, a winng system is connected to each of the elecfrode contacts 200. This is accomplished as shown m FIGS. 8 A, 8B, 8C and 8D. As seen in FIG. 8B, for example, an insulated wire 202', is laid on top of the elecfrode foil piece 220 (the cross bar of the "T"). The leg of the "T" of the foil piece 210 is then folded over to hold the end of the wire while the wire is welded in position (FIG. 8B). The welding process, preferably a resistance weld, burns away any insulation from the tip while making a secure mechanical and electπcal connection between the wire and the elecfrode contact 200. The result is an electrode contact 200 having a wire 202' securely attached thereto (FIG. 8C). If other wires are present, e.g., going to more distal electrode contacts, then such wires may pass over the foil piece 210, lying more or less parallel to the wire 202' so as to form a bundle of wires 202. A similar bundle may be formed on the other side of the folded foil piece 210, thereby forming another wire bundle 203. The ends of the foil piece 220 are then folded upwards to form, in one embodiment, a tπangle, or Δ shape (as seen in a side view), as shown in FIG. 8D. In another embodiment, they are folded upwards to form a U shape.

As seen in FIG. 8A, at least one wire from one of the bundles 202 or 203 is attached to the electrode contacts 2- 16 m the manner described above. (For simplicity, only six of the sixteen or nineteen elecfrode contacts used m the elecfrode aπay 30 or 30' are shown in FIG. 8 A,) Typically, a wire from wire bundle 202 will connect to electrode contact 16, and a wire from bundle 203 will connect to electrode contact 15, and so on, with adjacent m-line electrode contacts being connected to wires from alternating wire bundles. At least two wires, one from each bundle 202 and 203 remain for connection to the most distal electrode contact 1. In this fashion, at least seventeen wires are used to make elecfrical connection with sixteen elecfrode contacts. In the prefeπed embodiment, for example, the wire bundle 202 may contain 9 wires, and the wire bundle 203 may contain 8 wires, for the sixteen-electrode aπay 30 or 30' descnbed herein. The wire bundles 202 and 203 pass through the dummy elecfrode contacts, or reference marker contacts 34 (FIG. 1, 6), without making elecfrical contact therewith. For simplicity, the reference marker contacts 34 are not shown m FIG. 8A.

Having a wire bundle on each lateral side of each elecfrode contact, e.g., as seen m the sectional view of FIG. 5 A or 6B, and hence on each lateral side of the elecfrode array, helps add lateral stability to the aπay. This is true even when the wire "bundle" only contains one wire. Thus, an important feature associated with using two wire bundles in the manner descnbed is that the wire bundles help add stiffness to the electrode aπay in the lateral direction, but do not matenally affect the ability of the aπay to flex or bend m the medial direction.

Once the wire bundles 202 and 203 have been connected to all of the active electrodes 200, the foil earner 100 may be placed on a molding die 300 as shown m FIG. 9. The die 300 has alignment pegs 310 adapted to align with coπesponding alignment holes 110 m the foil earner 100. The die 300 further has a cavity or channel 320 formed therein into which the required amount of matenal, e.g., LSR-70, needed to form the polymer earner 36 (FIGS.4, 6) is injected. The LSR-70 is then cured in conventional manner. This cavity or channel 320 may be shaped or formed as desired. The mold depicted m FIG. 9 would form a straight earner 36

As an alternative to the flat-surface die 300 shown m FIG. 9, a curved die 301 is preferably used as shown in FIGS. 10 and 11. Such die 301 includes a curved surface 303 on a holding block 304 on which the foil earner 100 may be placed. The block 304 has alignment pegs 311 adapted to align with coπesponding alignment holes 110 m the foil earner 100. The foil caπier 100 is placed on the block 304 and bent over the curved surface 303. The die 301 is then placed over the block 304, with the foil earner 100 sandwiched therebetween. A channel or cavity 321 is formed in the die 301 having the desired shape and charactenstics of the earner that is to be formed through the molding process. The required amount of matenal to form the polymer caπier 36, e.g., LSR-70, is then injected into the channel and allowed to cure. By placing the foil earner assembly 100 in the curved die of FIGS. 10 and 11 (note that FIG. 10 comprises a perspective view of the die 301 and block 304, and FIG. 11 compnses a side or profile view of the die 301 and block 304), the aπay can be molded or formed to assume the desired curved shape. Such curved shape is prefeπed to achieve directional stability of the aπay dunng insertion.

Thus, it is seen that through proper use of the die 300 or 301/304, or other dies, the electrode aπay may be formed to assume a natural curved shape, a slightly curved shape, or to be straight. After the matenal used to form the earner (e.g., LSR-70) cures, the foil earner with the electrode aπay assembly (which is now molded inside of the polymer) is removed from the channel of the die 300 or 301/304 and placed in a mixture of diluted acids. The mixture of diluted acids dissolves the foil earner 100, thereby exposing a clean surface of the electrode contacts 200. After washing to remove any residue of acids and Fe salts, the mam electrode aπay structure is completed

Advantageously, the structure of the electrode aπay 30, as seen best in the sectional view of FIG. 5A, or the electrode aπay 30', as seen best m the sectional view of FIG. 6B, bends or flexes more easily in the medial direction than in the late al direction. That is, the elecfrode aπay, with its slight curved shaped, when inserted into the cochlea, is able to bend, as required, to follow the scala tympani duct of the cochlea (whether the nght or left cochlea) as it is inserted deeper and deeper into such duct. As it does so, the electrode contacts 32 remain closest to and facing the modiolus wall, as desired. As the elecfrode aπay is inserted deeper into the cochlea, the electrode aπay does not easily twist, or bend laterally, which twisting or bending could move the electrode contacts away from the modiolus wall. This is because the electrode aπay is inherently stiffer rn the lateral direction than m the medial direction due pnmanly to the presence of the wire bundles and folded/bent electrode contacts which provide an added degree of stiffness m the lateral direction.

To further understand one mechanism by which the present invention achieves flexing or bending in the medial direction, but resists such bending m a lateral direction (where the "medial" direction may be defined as the direction m which the elecfrode contacts face, and the "lateral direction" may be defined as a direction perpendicular to both the medial direction and a longitudinal axis of the aπay), consider the following simplified model of the electrode aπay: The electrode contacts 32 may be viewed as ngid rectangular plates, hmged together by the flexible earner matenal and wire bundles between each plate. Thus, sixteen such plates are hmged together in a long chain, each plate in the chain being connected to an adjacent plate in the chain by way of a hmged connection. Such chain of "hmged plates" may readily pivot about their respective hinged connections, thus easily and readily allowing the chain of hmged plates to bend m the medial direction. However, due to the ngid nature of each plate, bending m the lateral direction, assuming a perfect hmged connection, is virtually impossible. Even assuming a less-than-perfect hinged connection, bending m the lateral direction is still made difficult. This is because fixed-length wire bundles are embedded m the earner on opposite lateral sides of the aπay. These "matched" (of equal length) wire bundles tend to make lateral bending or flexing more difficult because such lateral flexmg or bending would typically require that one of the wire bundles increase in length, as the other decreases in length, as a lateral bend is made. Because the elecfrode contacts of the elecfrode aπay disclosed herein remain facing and closest to the modiolar wall, stimulation of the cells embedded within the modiolar wall occurs at lower energy settings than would be required if the electrode contacts were not facing and closest to the modiolar wall. Hence, use of the present elecfrode aπay allows desired stimulation to be achieved at lower power levels. Lower power levels, in turn, mean that the overall cochlear stimulation system may operate on less power, which means a longer interval between battery replacement.

As described above, it is thus seen that the present invention provides an electrode aπay that is easy to manufacture and which provides enhanced performance when used. Such electrode aπay provides an aπay of spaced-apart elecfrodes along the medial side of the aπay. Upon insertion into the cochlea, the elecfrode contacts all face the modiolus wall. The composition and makeup of the electrode aπay makes it easier to bend in the medial direction than in a sideways or lateral direction. Thus, the electrode contacts remain on the medial side of the electrode, which medial side remains closest to the modiolus wall when the elecfrode is inserted into the cochlea.

While the invention herein disclosed has been described by means of specific embodiments and applications thereof, numerous modifications and variations could be made thereto by those skilled in the art without departing from the scope of the invention set forth in the claims.

Claims

CLAIMSWhat is claimed is:

1. An implantable electrode aπay (30) for use with a tissue stimulation device compnsmg a flexible earner (36) having a medial side; a multiplicity of in-line elecfrodes (32) having an exposed surface area only on the medial side of the flexible earner, the elecfrodes having an embedded portion (220) behmd the exposed contact surface area that extends into the flexible earner; and a multiplicity of wires (202, 203) embedded withm the flexible earner, at least one wire of the multiplicity of wires being electncally and physically connected to a respective m-line electrode, and each wire of the multiplicity of wires not electncally connected to an inline elecfrode being engaged by the embedded portion of the m-hne electrode it passes by; wherein the elecfrode aπay is more flexible in a medial direction than in a direction lateral to the medial direction, where the medial direction compnses the direction faced by the exposed contact surface area of the in-line electrodes.

2. The implantable elecfrode aπay of Claim 1 wherein each in-line electrode compnses first and second metallic stnps (210, 220) formed in a "T" shape, wherein a leg of the "T" is folded back over itself and holds at least one of the multiplicity of wires therebetween, the at least one wire being electncally bonded to the folded T leg, and wherein sides of the "T" are folded upwardly into the flexible earner.

3. The implantable electrode aπay of Claim 2 wherein the multiplicity of wires not electncally connected to an in-line elecfrode pass over the folded up sides of the "T".

4. The implantable elecfrode aπay of Claim 3 wherein the folded up sides of the "T" form a "Δ" shape, the folded up sides of the "Δ" compnsmg the embedded portion of the electrode, and wherein the multiplicity of wires are grouped into first and second wire bundles, the first wire bundle passing through one side of the "Δ", and the second wire bundle passing through the other side of the "Δ".

5 The implantable electrode aπay of Claim 3 wherein the folded up sides of the "T" form a "U" shape, the folded up sides of the "U" compnsmg the embedded portion of the electrode, and wherein the multiplicity of wires are grouped into first and second wire bundles, the first wire bundle passing through one side of the "U", and the second wire bundle passing through the other side of the "U"

6 The implantable electrode aπay of Claim 1 wherein the multiplicity of m-line electrodes compnses n electrodes, where n is an integer of at least 8, and wherein a most distal electrode compnses a first electrode, and wherein a most proximal electrode compnses an nth electrode.

7 The implantable electrode aπay of Claim 6 wherein the multiplicity of wires compnses at least n+l wires, at least one wire being connected to each of the second through nth electrodes, and at least two wires being connected to the first electrode.

8. The implantable electrode aπay of Claim 7 wherein the at least n+l wires are separated into two bundles, a first bundle being routed up one lateral side of the electrode aπay and a second bundle being routed up the other lateral side of the electrode aπay, wherein both wire bundles are engaged by the m-line electrodes they pass by, and wherein both wire bundles are embedded withm the flexible earner, and wherein at least one wire connected to the first electrode comes from the first bundle, and wherein at least one wire connected to the first electrode comes from the second wire bundle.

9. The implantable elecfrode aπay of Claim 1 further including a hump formed on the medial side of the aπay m the space between the flat rectangular contact surface area of each electrode.

10 The implantable elecfrode aπay of Claim 9 wherein the flexible earner is made from a sihcone rubber material of a first hardness, and the humps are made from a sihcone rubber matenal of a second hardness, where the first hardness is harder than the second hardness

11 The implantable elecfrode aπay of Claim 10 further including a soft tip formed at a distal end of the flexible caπier, the soft distal tip being made from the sihcone rubber matenal having the second hardness.

12. The implantable electrode aπay of Claim 11 wherein the soft tip is formed m a ball shape, and wherein the ball- shaped soft tip functions as a bumper to prevent tissue damage as the electrode aπay is inserted into a curved body cavity.

13. The implantable electrode aπay of Claim 1 wherein the electrode aπay compnses an implantable cochlear electrode aπay adapted for insertion into a human cochlea, and wherein each electrode has an exposed contact surface area that is rectangular in shape.

14. The implantable electrode aπay of Claim 13 wherein the exposed surface area of each electrode is substantially flat, having a surface area of approximately 0.16 mm² or more..