CA1332444C - Ring electrode for multiconductor pacing leads - Google Patents
Ring electrode for multiconductor pacing leadsInfo
- Publication number
- CA1332444C CA1332444C CA000600478A CA600478A CA1332444C CA 1332444 C CA1332444 C CA 1332444C CA 000600478 A CA000600478 A CA 000600478A CA 600478 A CA600478 A CA 600478A CA 1332444 C CA1332444 C CA 1332444C
- Authority
- CA
- Canada
- Prior art keywords
- sleeve
- insulative
- electrode
- coil
- conductor
- 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.)
- Expired - Fee Related
Links
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
-
- 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
Abstract
RING ELECTRODE FOR MULTICONDUCTOR PACING LEADS
ABSTRACT
A cardiac pacing lead having a plurality of individually insulated conductors arranged as a multifilar coil. The lead includes a connector assembly and a ring electrode assembly, each of which are optimized for use in conjunction with conductors arranged in the form of a multifilar coil. The connector assembly takes the form of an in-line connector having a plurality of linearly arranged connecting surfaces, each coupled to one of the conductors in the multifilar coil. The ring electrode assembly is constructed such that it displays the same outer diameter as the pacing lead. In both assemblies, conductors are coupled by means of welds, rather than by crimping or swaging.
ABSTRACT
A cardiac pacing lead having a plurality of individually insulated conductors arranged as a multifilar coil. The lead includes a connector assembly and a ring electrode assembly, each of which are optimized for use in conjunction with conductors arranged in the form of a multifilar coil. The connector assembly takes the form of an in-line connector having a plurality of linearly arranged connecting surfaces, each coupled to one of the conductors in the multifilar coil. The ring electrode assembly is constructed such that it displays the same outer diameter as the pacing lead. In both assemblies, conductors are coupled by means of welds, rather than by crimping or swaging.
Description
~ 3 32 ~ ~66742-305 BACKGROUND OF INVENTION
The present invention relates to medical electrical leads generally, and more particularly to cardiac pacing leads. ~
Early pacing leads, such as those disclosed in United -States Patent No. 3,348,548 and United States Patent No. 3,788,329 employed separate conductor coils in a side-by-side or coaxial configuration, insulated from one another by plastic sheaths which covered the coils. More recently, multifilar coiled conductors having individually insulated coil wires have been pursued, as disclosed in Canadian Patent No. 1,146,228 for a MULTIPOLAR PACING
CONDUCTOR, issued May 10, 1983 to Upton. This patent discloses a single, multiconductor DBS coil having individually insulated wires.
BUMMARY OF THE INVENTION
The present invention is directed toward optimizing the construction of a pacing lead or other medical electrical lead of the type employing multiple, mutually insulated conductors, arrang-ed in the form of a multipolar coil. In particular, the invention is directed toward improved connector assemblies and ring elec- ;
trode assemblies for such leads.
Typically, in pacing leads employing a plurality of conductors, each of which are formed as a separate coil, connection ;
of the coil toian electrode or a connector pin has been accom~
plished by means of crimping or swaging these components to one another, as disclosed in United States Patent No. 4,258,725, issued to O'Neill and United States Patent No. 4,328,812, issued ~ ., ' ':' - 2 ~ ~ 332~ 66742 305 to Ufford et al. However, where the conductors take the form of a multifilar coil, additional problems are presented. The con-ductors must be split off from the coil, individually, and routed to the desired connector surface or electrode surface, without compromising the mechanical integrity of the lead at that point.
Because one of the advantages of a multiconductor coil is that it allows fabrication of a smaller diameter lead, it is especially desirable to avoid unnecessary bulk in the vicinity of these assemblies. ~;
The present invention addresses these problems by pro-viding connector and electrode assemblies which are constructed to allow all electrical connections to the conductors to be made ;
by welding. This allows for the elimination of crimping or swaging cores commonly used in prior art leads. In addition, the connec-tor and ring electrode assemblies are designed to pro~ide increased ;
structural integrity and improved sealing due to the use of hot-melt and adhesive backfill procedures during manufacture.
According to a broad aspect of the invention there is ; ;
provided a ring electrode assembly for use in a medical electrical lead, comprising: an elongated coiled conductor; an elongated, insulative sleeve having a proximal end and a distal end, said sleeye bonded to and conforming to the outer surface of said conductor coil; a cylindrical electrode ring mounted coaxially about said insulative sleeve, such that the proximal and distal ends of said insulative sleeve extend from said cylindrical electrode, said cylindrical electrode electrically coupled to said . ~ :
~ 3 ~ 1 3 3 2 ~ ~ ~ 66742-305 conductor coil, said cylindrical electrode bonded to the outer surface of said insulative sleeve; first insulative sheath extend-ing proximally from said cylindrical electrode, said first insulative sheath bonded to and surrounding the exterior of said proximal end of said insulative sleeve; and second insulative sheath extending distally from said cylindrical electrode, said second insulative sheath bonded to and surrounding the distal end of said insulative sleeve.
According to another broad aspect of the invention there is provided a method for fabricating an electrode for a medical electrical lead, comprising the steps of: selecting a multifilar coil having at least two conductors and terminating one of the conductors intermediate the ends of the coil; selecting a generally cylindrical sleeve of a thermoplastic material, having ~.
an internal lumen and a bore perpendicular to the internal lumen and sliding said sleeve over said multifilar coil and bringing the end of said terminated conductor out through said bore; placing .
said sleeve and coil into a mold and applying heat, causing said sleeve to bond to said multifilar coil and to flow between the conductors of said multifilar coil; sliding a cylindrical ring electrode over said sleeve intermediate the proximal and distal ends of said sleeve and electrically coupling said end of said :
I , i I , : .
terminated conductor to said cylindrical electrode î and sliding first and second insulative sheaths over the proximal and distal ends of said sleeve, respecti~ely, placing said ring electrode and the ends of said first and second sleeves into a mold and : ` :
4 _ ~ 3 3 ~ 66742-305 ""
applying heat to bond said sleeve to said electrode and to said first and second sheaths.
BRIEF DESCRIPTION OF THE DRAWINGS
Figure 1 shows a plan view of a bipolar cardiac pacing lead according to the present inv,ention.
Figure 2 shows a sectional view of the lead of Figure 1 in the vicinity of the connector assembly.
Figu~e 3 shows an alternative connector assembly for ;~
, ~ ..
use with a tripolar lead.
Figure 4 shows a sectional view of the lead of Figure 1 ;~;~
in the vicinity of the ring electrode.
DETAILED DESCRIPTION OF THE DRAWINGS ~,-Figure 1 is a plan view of a pacing lead employing improvements according to the present invention. At the distal end of the lead is located a pacing electrode 10, which may be fabricated according to any of a variety of well known electrode types. Preferably, the electrode is fabricated according to the disclosure in United States Patent No. 4,506,680, issued to Stokes.
,..: . :: ;.
Electrode 10 is held in place within the heart by means of pliant tines 12, which are more fully described in United States Patent No. 3,902,501, issued to Citron et al. -The lead includes an elongated insulative sheath 14, which extends from the connector assembly 16 to the ring electrode 18. The lead also includes a second insulative sheath 20, extend~
ing from ring electrode 18 to electrode 10. Mounted around insulative sheath 14 is a suture sleeve 17, which is used to anchor . ::, :
- 4a - 1 3 3 2 ~ 4466742_305 the lead at the point of venous insertion. Connector assembly 16 includes a connector pin 24 and a connector ring assembly compris-ing an exposed ring shaped member 22. Insulative sleeve 26 separates pin 24 from ring member 22. Insulative sleeve 28 extends distal to ring member 22. The connector assembly is provided with resiliant sealing rings 30 and 32, which seal the connector assem-bly within a corresponding receptacle mounted to a cardiac pace-maker. The area of the lead enclosed by dashed line 34 is illustrated in more detail in Figure 2. The area of the lead enclosed by dashed line 36 is illustrated in more detail in Figure;
4.
Insulative sleeves 26 and 28 are preferably fabricated of silicone rubber. Insulative sheaths 14 and 20, are preferably fabricated of polyurethane or silicone rubber. Connector pin 24, ring member 22, ring electrode 18 and tip electrode 10 are preferably fabricated of inert conductive metals such as platinum, Elgiloy ~ alloy, MP35N or stainless steel.
Figure 2 shows a sectional view of the proximal portion of connector assembly 16, illustrated in Figure 1. This view ;
shows the interconnection of the multiconductor coil 34 with the other components of connector assembly 16, illustrated in Figure ~
1. Components visible in Figure 1 are labeled similarly in Figure ~ -2. Multiconductor coil 34 includes a first coiled conductor ~`
coupled to connector pin 24 and a second coiled conductor elec-trically coupled to ring member 22.
The connector assembly is fabricated by first laser i :.: .. ' ' ' ... ' .. ~ . . ' ' ' . " , .' . , '~, " ' ' ' ... .. ... ... .... .
- 4b - 1 3 3~ 66742_305 welding ring member 22 to cylindrical member 36 by means of a circumferential laser weld at 38 to form a connector ring assembly. ~ ;~
Assembled ring member 22 and cylindrical member 36 are assembled over connector pin 24, placed into a mold, and insulative sleeve 26 is then injection molded between them. This process is dis-closed in more detail in United States Patent No. 4,572,605, issued to Hess.
The completed assembly of connector pin 24, insulative sleeve 26, ring member 22 and tubular member 36 is then coupled to -one conductor 40 of multiconductor coil 34. Conductor 40 is ;
screwed onto the distal end of connector pin 24, with protrusion 42 acting as a screw thread. Conductor 40 is screwed onto connec- ;
tor pin 24 until its proximal end butts up against circular flange 44. Conductor 40 is then coupled to circular flange 44 at 46 by means of a spot laser weld. The spacing intermediate circular ~;
flange 44 and protrusion 42 allows for a limited amount of strain relief immediately distal to the spot laser weld at 46. ~
Tubular extension 48, which takes the form of a cylin- - ;:
der having an extended longitudinal slot 50 is then slid over the distal end of cylindrical member 36 and coupled to it by means of a circumferential laser weld at 52. A shallow grooved section 52, having a groove that corresponds generally to the size of conductor 54, is located at the proximal end of slot 50 in tubular extension -48. Conductor 54 is stripped of insulation and laid lengthwise in the grooved area 52, and laser welded to extension 48. Following this step, insulative sleeve 28 is slid over extension 48 and over : ~
: .......
-.: .: i `: :
- 4c - 1 3 3 2 ~ ~ ~ 66742-305 cylindrical member 36. Member 36 is provided with a cross bore 56, which may be filled with medical adhesive, thereby bonding insulative sleeve 28 to insulative sleeve 26.
Finally, the entire assembly is backfilled with adhesive injected between insulative sheath 14 and .:
~, .
' ~
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' "
' --~
~ 3 ~ 2 ~
-5~
insulative sleeve 28, filling the area between insulative sleeve 28 and sheath 14, as well as the lumen 58 of sleeve 28 and the lumen 60 of tubular extension 48. This serves to bond the components of the connector assembly to one 5 another and to insulative sleeve 28 and to electrically insulate the conductor 40 and connector pin 24 from the conductor 54. For the sake of clarity, the backfilled ~ `
adhesive is not shown in this illustration. Mounted ~--within multiconductor coil 34 is a Teflon~ plastic liner -10 62, which serves as a passageway for a stylet. The internal lumen of liner 62 is aligned with the internal bore 64 of connector pin 24.
Fig. 3 shows an alternative connector assembly ~
adapted for use with a tripolar, coaxial lead. This~ -15 figure illustrates how sequential application of the basic techniques disclosed in conjunction with the bipolar lead can be used to produce a tripolar or multipolar connector having sequential, ring shaped connector surfaces.
The connector assembly of Fig. 3 is fabricated by 20 first assembling connector ring 122 over connector pin 124, placing them in a mold and subsequently injection molding insulative sleeve 126 between them. This process is disclosed in the above cited Hess patent. Connector pin 124 is provided with a lumen 120 through which a 25 stylet may be inserted. Connector ring 122 is provided with two perpendicular bores 123 which are filled by sleeve 126 during the molding procedure. The assembly of connector pin 124, sleeve 126 and connector ring 122 is ~
then coupled to the inner conductor coil 140. Conductor ;
30 coil 140 is slipped over the distal end of connector pin 124, and held in place by means of crimping sleeve 142.
Insulative sleeve 141 is then slid over inner conductor 140.
After attachment of inner conductor 140 to the distal 35 end of connector pin 124, tubular extension 148, which takes the form of a cylinder having a longitudinal slot 150 at its distal end and second connector ring 200 are -6- 1 3 3 2 ~
assembled in their respective positions in an injection mold, and insulative sleeve 202 is injection molded between them. Connector ring 200 is provided with two perpendicular bores 201 which are filled by sleeve 202 5 during the molding process. This assembly is then slid over the distal end of connector ring 122 and coupled to it by means of a circumferential laser weld at 152. After this step, the proximal ends of two of the individual conductor wires 135 of multifilar coil 134 are stripped of 10 insulation and laser welded to tubular extension 148 in slot 150. Following this step, a second tubular extension 204 is slid over tubular extension 148. Second tubular extension 204 is welded to second connector ring 200 by means oE a circumferential laser weld at 203. Tubular 15 extension 204 includes an elongated slot 208 and a shallow grooved section 210 at its distal end. The proximal ends of the two other conductors 137 from multipolar coil 134 are stripped, laid in shallow groove 210 and laser welded within groove 210. Outer insulative sheath 220 is then 20 slid over multipolar coil 134.
After these steps have been completed, a sealing ring/strain relief member 212 is applied around the second connector ring 200. Because of the penetration of the material of sleeve 202 through bores 201, member 212 can -25 be bonded directly to insulating sleeve 202 using a suitable adhesive. This provides a better bond than would be available if member 212 were bonded directly to connector ring 200. If sleeve 202 and sealing ring member 212 are both fabricated of silicone rubber, a silicone~ -~
30 medical adhesive would be appropriate.
The interior of the assembly is backfilled with silicone adhesive 222 through bore 224, which extends through second connector ring 200, sleeve 202 and tubular extension 148. Backfilling continues until the adhesive 35 is visible within the lumen of sealing ring/strain relief member 212, distal to tubular extension 204. This seals the lead, provides additional electrical insulation, and 133 2~4 66742-305 -:, internally bonds the components together for added mechanical strength.
A second sealing ring member 214 is applied exterior to first connector ring 122. Because sleeve 126 extends through bores 123, sealing ring member 214 may be bonded directly to sleeve 126, using a suitable adhesive.
Surrounding sealing ring strain relief member 214 is a locking sleeve 218, which is intended to be used in conjunction with a deflectable beam locking member on the connector housing into which the lead is inserted. ~
Connector rin~s 122 and 200, connector pin 124, ;
tubular extensions 148 and 204 and crimp sleeve 142 may all be fabricated of an inert, biocompatible metal such as stainless -~
steel. Sleeves 126 and 202 and sealing ring members 212 and 214 are preferably fabricated of silicone rubber. Sheaths 141 and 220 and locking sleeve 218 are preferably fabricated of polyether urethane.
By repeated duplications of the connector rings, insulating sleeves and tubular extensions, a connector assembly -having any number of linearily arranged connector rings may be produced. The particular configuration of the components allows -for Ithe use of laser or resistance welding to accomplish all metal to metal connections, leading to i~creased reliability and improved reproducibility during production. Therefore, both the method of fabrication of this connector assembly and the resultant product are believed to be a substantial improvement over :, .: 66742-305 1332~44 ~:
previous in-line connector designs. :
Figure 4 shows a sectional view of the area adja-cent the ring electrode 18, illustrated in Figure 1. In this view, the interconnection of the conductor 54 and ring elec-trode 18 is illustrated. Ring electrode 18 takes the - 7a -~'~
1332~
form of a metal cylindrical tube, having a slot 64 adjacent its distal end. The stripped end of conductor 54 is laser welded to the end of slot 64 in electrode 18 at 66. This provides the electrical connection between the 5 conductor and the ring electrode. The mechanical connection between the various parts of the electrode is provided by means of a plastic sleeve 66, which is preferably fabricated of Pellethane0 2363-80A polyether urethane. Pellethane~ 2363-55D polyether urethane may 10 also be used.
The ring electrode 18 is accomplished by first sliding sleeve 66 over the multifilar coil 34. Conductor , 54 is brought out through a hole in sleeve 66. Then the assembly of coil 34 and sleeve 66 is inserted into a 15 cylindrical mold having a diameter slightly less than the inner diameter of the ring electrode 18. Heat is applied, causing the insulative sleeve to heat bond to multifilar coil 34. This also causes sleeve 66 to flow between the conductors of multifilar coil 34, stabilizing it in the 20 area of the electrode. Ring electrode 18 is slid over sleeve 66, and the stripped end of conductor 54 is laser welded to ring electrode 18 at 69. At the ends of sleeve 66, medical adhesive 68 and 70 is provided, bonding the ~ ;
insulative sleeve 66 to the multifilar coil 34 and to the 25 liner 62. This structure provides mechanical integrity to the assembly and acts as a strain relief. Insulative sheaths 14 and 20 are then slid over the ends of ;
insulating sleeve 66, and the assembly is inserted into a cylindrical mold having a diameter corresponding to the 30 outer diameter of ring electrode 18. Heat is applied, causing insulative sleeve 66 to heat bond to ring electrode 18 and to insulative sleeves 14 and 20. The resultant structure provides a lead having a uniform outer diameter in the vicinity of the ring electrode. The 35 bonding of sleeve 66 to sheaths 14 and 20 provides a continuous electrically insulative and fluid tight tube ~ ' ~,~
:' g i33~
which extends the length of the lead. During heating, sleeve 65 also collapses around conductor 54, sealing this potential point of fluid entry as well. Slot 64 in ring electrode 18 is filled with medical adhesive 70, to S complete the assembly. In order to improve the mechanical interconnection of the components of the lead, the Tefzel~9 plastic insulation of the multiconductor coil 34 and Teflon~ plastic tubing 62 are treated with Chemgrip or by glow discharge (plasma) to activate their surfaces to 10 enhance adhesion to the sleeve 66 and to silicone medical adhesive 70. A polyurethane glue, comprised of Pellethane0 2363-75D in N,N-dimethyl acetamide, is applied to the sleeve 66 and subsequently air dried to ehance adhesion to silicone medical adhesive. Adhesion 15 promoters, such as Dow Corning~ Z-6020 silane (amino alkyl functional silane), may be applied to metal or plastic components prior to the application of medical adhesive to further improve the mechanical interconnection of the lead components.
The resulting assembly provides a structure which is tightly sealed against fluid entry, and which displays a high tensile strength through the area of the ring electrode. This structure also provides a gradual transition in flexibility from the ring electrode 18 25 proximally and distally, through the combination of sleeve 66 and adhesive 68 and 70. In addition, the structure allows for the fabrication of a substantially smaller diameter ring electrode than possible using assemblies ;
which require crimping or swaging cores, as disclosed in U.S. Patent No. 4,328,812, issued to Ufford et al, discussed above.
Although the particular embodiment disclosed in this application takes the form of a cardiac pacing lead, the - ~
inventions disclosed herein are believed equally ~-35 applicable to medical electrical leads in general. In conjunction with the above description, we claim:
,~
. , . . , .. . , . . , . . . . ,, . ..... . .. .. . .. . . ... . . , . ~ .. .. . . .. . . . .
The present invention relates to medical electrical leads generally, and more particularly to cardiac pacing leads. ~
Early pacing leads, such as those disclosed in United -States Patent No. 3,348,548 and United States Patent No. 3,788,329 employed separate conductor coils in a side-by-side or coaxial configuration, insulated from one another by plastic sheaths which covered the coils. More recently, multifilar coiled conductors having individually insulated coil wires have been pursued, as disclosed in Canadian Patent No. 1,146,228 for a MULTIPOLAR PACING
CONDUCTOR, issued May 10, 1983 to Upton. This patent discloses a single, multiconductor DBS coil having individually insulated wires.
BUMMARY OF THE INVENTION
The present invention is directed toward optimizing the construction of a pacing lead or other medical electrical lead of the type employing multiple, mutually insulated conductors, arrang-ed in the form of a multipolar coil. In particular, the invention is directed toward improved connector assemblies and ring elec- ;
trode assemblies for such leads.
Typically, in pacing leads employing a plurality of conductors, each of which are formed as a separate coil, connection ;
of the coil toian electrode or a connector pin has been accom~
plished by means of crimping or swaging these components to one another, as disclosed in United States Patent No. 4,258,725, issued to O'Neill and United States Patent No. 4,328,812, issued ~ ., ' ':' - 2 ~ ~ 332~ 66742 305 to Ufford et al. However, where the conductors take the form of a multifilar coil, additional problems are presented. The con-ductors must be split off from the coil, individually, and routed to the desired connector surface or electrode surface, without compromising the mechanical integrity of the lead at that point.
Because one of the advantages of a multiconductor coil is that it allows fabrication of a smaller diameter lead, it is especially desirable to avoid unnecessary bulk in the vicinity of these assemblies. ~;
The present invention addresses these problems by pro-viding connector and electrode assemblies which are constructed to allow all electrical connections to the conductors to be made ;
by welding. This allows for the elimination of crimping or swaging cores commonly used in prior art leads. In addition, the connec-tor and ring electrode assemblies are designed to pro~ide increased ;
structural integrity and improved sealing due to the use of hot-melt and adhesive backfill procedures during manufacture.
According to a broad aspect of the invention there is ; ;
provided a ring electrode assembly for use in a medical electrical lead, comprising: an elongated coiled conductor; an elongated, insulative sleeve having a proximal end and a distal end, said sleeye bonded to and conforming to the outer surface of said conductor coil; a cylindrical electrode ring mounted coaxially about said insulative sleeve, such that the proximal and distal ends of said insulative sleeve extend from said cylindrical electrode, said cylindrical electrode electrically coupled to said . ~ :
~ 3 ~ 1 3 3 2 ~ ~ ~ 66742-305 conductor coil, said cylindrical electrode bonded to the outer surface of said insulative sleeve; first insulative sheath extend-ing proximally from said cylindrical electrode, said first insulative sheath bonded to and surrounding the exterior of said proximal end of said insulative sleeve; and second insulative sheath extending distally from said cylindrical electrode, said second insulative sheath bonded to and surrounding the distal end of said insulative sleeve.
According to another broad aspect of the invention there is provided a method for fabricating an electrode for a medical electrical lead, comprising the steps of: selecting a multifilar coil having at least two conductors and terminating one of the conductors intermediate the ends of the coil; selecting a generally cylindrical sleeve of a thermoplastic material, having ~.
an internal lumen and a bore perpendicular to the internal lumen and sliding said sleeve over said multifilar coil and bringing the end of said terminated conductor out through said bore; placing .
said sleeve and coil into a mold and applying heat, causing said sleeve to bond to said multifilar coil and to flow between the conductors of said multifilar coil; sliding a cylindrical ring electrode over said sleeve intermediate the proximal and distal ends of said sleeve and electrically coupling said end of said :
I , i I , : .
terminated conductor to said cylindrical electrode î and sliding first and second insulative sheaths over the proximal and distal ends of said sleeve, respecti~ely, placing said ring electrode and the ends of said first and second sleeves into a mold and : ` :
4 _ ~ 3 3 ~ 66742-305 ""
applying heat to bond said sleeve to said electrode and to said first and second sheaths.
BRIEF DESCRIPTION OF THE DRAWINGS
Figure 1 shows a plan view of a bipolar cardiac pacing lead according to the present inv,ention.
Figure 2 shows a sectional view of the lead of Figure 1 in the vicinity of the connector assembly.
Figu~e 3 shows an alternative connector assembly for ;~
, ~ ..
use with a tripolar lead.
Figure 4 shows a sectional view of the lead of Figure 1 ;~;~
in the vicinity of the ring electrode.
DETAILED DESCRIPTION OF THE DRAWINGS ~,-Figure 1 is a plan view of a pacing lead employing improvements according to the present invention. At the distal end of the lead is located a pacing electrode 10, which may be fabricated according to any of a variety of well known electrode types. Preferably, the electrode is fabricated according to the disclosure in United States Patent No. 4,506,680, issued to Stokes.
,..: . :: ;.
Electrode 10 is held in place within the heart by means of pliant tines 12, which are more fully described in United States Patent No. 3,902,501, issued to Citron et al. -The lead includes an elongated insulative sheath 14, which extends from the connector assembly 16 to the ring electrode 18. The lead also includes a second insulative sheath 20, extend~
ing from ring electrode 18 to electrode 10. Mounted around insulative sheath 14 is a suture sleeve 17, which is used to anchor . ::, :
- 4a - 1 3 3 2 ~ 4466742_305 the lead at the point of venous insertion. Connector assembly 16 includes a connector pin 24 and a connector ring assembly compris-ing an exposed ring shaped member 22. Insulative sleeve 26 separates pin 24 from ring member 22. Insulative sleeve 28 extends distal to ring member 22. The connector assembly is provided with resiliant sealing rings 30 and 32, which seal the connector assem-bly within a corresponding receptacle mounted to a cardiac pace-maker. The area of the lead enclosed by dashed line 34 is illustrated in more detail in Figure 2. The area of the lead enclosed by dashed line 36 is illustrated in more detail in Figure;
4.
Insulative sleeves 26 and 28 are preferably fabricated of silicone rubber. Insulative sheaths 14 and 20, are preferably fabricated of polyurethane or silicone rubber. Connector pin 24, ring member 22, ring electrode 18 and tip electrode 10 are preferably fabricated of inert conductive metals such as platinum, Elgiloy ~ alloy, MP35N or stainless steel.
Figure 2 shows a sectional view of the proximal portion of connector assembly 16, illustrated in Figure 1. This view ;
shows the interconnection of the multiconductor coil 34 with the other components of connector assembly 16, illustrated in Figure ~
1. Components visible in Figure 1 are labeled similarly in Figure ~ -2. Multiconductor coil 34 includes a first coiled conductor ~`
coupled to connector pin 24 and a second coiled conductor elec-trically coupled to ring member 22.
The connector assembly is fabricated by first laser i :.: .. ' ' ' ... ' .. ~ . . ' ' ' . " , .' . , '~, " ' ' ' ... .. ... ... .... .
- 4b - 1 3 3~ 66742_305 welding ring member 22 to cylindrical member 36 by means of a circumferential laser weld at 38 to form a connector ring assembly. ~ ;~
Assembled ring member 22 and cylindrical member 36 are assembled over connector pin 24, placed into a mold, and insulative sleeve 26 is then injection molded between them. This process is dis-closed in more detail in United States Patent No. 4,572,605, issued to Hess.
The completed assembly of connector pin 24, insulative sleeve 26, ring member 22 and tubular member 36 is then coupled to -one conductor 40 of multiconductor coil 34. Conductor 40 is ;
screwed onto the distal end of connector pin 24, with protrusion 42 acting as a screw thread. Conductor 40 is screwed onto connec- ;
tor pin 24 until its proximal end butts up against circular flange 44. Conductor 40 is then coupled to circular flange 44 at 46 by means of a spot laser weld. The spacing intermediate circular ~;
flange 44 and protrusion 42 allows for a limited amount of strain relief immediately distal to the spot laser weld at 46. ~
Tubular extension 48, which takes the form of a cylin- - ;:
der having an extended longitudinal slot 50 is then slid over the distal end of cylindrical member 36 and coupled to it by means of a circumferential laser weld at 52. A shallow grooved section 52, having a groove that corresponds generally to the size of conductor 54, is located at the proximal end of slot 50 in tubular extension -48. Conductor 54 is stripped of insulation and laid lengthwise in the grooved area 52, and laser welded to extension 48. Following this step, insulative sleeve 28 is slid over extension 48 and over : ~
: .......
-.: .: i `: :
- 4c - 1 3 3 2 ~ ~ ~ 66742-305 cylindrical member 36. Member 36 is provided with a cross bore 56, which may be filled with medical adhesive, thereby bonding insulative sleeve 28 to insulative sleeve 26.
Finally, the entire assembly is backfilled with adhesive injected between insulative sheath 14 and .:
~, .
' ~
~ I ! ` I . ! I .
' "
' --~
~ 3 ~ 2 ~
-5~
insulative sleeve 28, filling the area between insulative sleeve 28 and sheath 14, as well as the lumen 58 of sleeve 28 and the lumen 60 of tubular extension 48. This serves to bond the components of the connector assembly to one 5 another and to insulative sleeve 28 and to electrically insulate the conductor 40 and connector pin 24 from the conductor 54. For the sake of clarity, the backfilled ~ `
adhesive is not shown in this illustration. Mounted ~--within multiconductor coil 34 is a Teflon~ plastic liner -10 62, which serves as a passageway for a stylet. The internal lumen of liner 62 is aligned with the internal bore 64 of connector pin 24.
Fig. 3 shows an alternative connector assembly ~
adapted for use with a tripolar, coaxial lead. This~ -15 figure illustrates how sequential application of the basic techniques disclosed in conjunction with the bipolar lead can be used to produce a tripolar or multipolar connector having sequential, ring shaped connector surfaces.
The connector assembly of Fig. 3 is fabricated by 20 first assembling connector ring 122 over connector pin 124, placing them in a mold and subsequently injection molding insulative sleeve 126 between them. This process is disclosed in the above cited Hess patent. Connector pin 124 is provided with a lumen 120 through which a 25 stylet may be inserted. Connector ring 122 is provided with two perpendicular bores 123 which are filled by sleeve 126 during the molding procedure. The assembly of connector pin 124, sleeve 126 and connector ring 122 is ~
then coupled to the inner conductor coil 140. Conductor ;
30 coil 140 is slipped over the distal end of connector pin 124, and held in place by means of crimping sleeve 142.
Insulative sleeve 141 is then slid over inner conductor 140.
After attachment of inner conductor 140 to the distal 35 end of connector pin 124, tubular extension 148, which takes the form of a cylinder having a longitudinal slot 150 at its distal end and second connector ring 200 are -6- 1 3 3 2 ~
assembled in their respective positions in an injection mold, and insulative sleeve 202 is injection molded between them. Connector ring 200 is provided with two perpendicular bores 201 which are filled by sleeve 202 5 during the molding process. This assembly is then slid over the distal end of connector ring 122 and coupled to it by means of a circumferential laser weld at 152. After this step, the proximal ends of two of the individual conductor wires 135 of multifilar coil 134 are stripped of 10 insulation and laser welded to tubular extension 148 in slot 150. Following this step, a second tubular extension 204 is slid over tubular extension 148. Second tubular extension 204 is welded to second connector ring 200 by means oE a circumferential laser weld at 203. Tubular 15 extension 204 includes an elongated slot 208 and a shallow grooved section 210 at its distal end. The proximal ends of the two other conductors 137 from multipolar coil 134 are stripped, laid in shallow groove 210 and laser welded within groove 210. Outer insulative sheath 220 is then 20 slid over multipolar coil 134.
After these steps have been completed, a sealing ring/strain relief member 212 is applied around the second connector ring 200. Because of the penetration of the material of sleeve 202 through bores 201, member 212 can -25 be bonded directly to insulating sleeve 202 using a suitable adhesive. This provides a better bond than would be available if member 212 were bonded directly to connector ring 200. If sleeve 202 and sealing ring member 212 are both fabricated of silicone rubber, a silicone~ -~
30 medical adhesive would be appropriate.
The interior of the assembly is backfilled with silicone adhesive 222 through bore 224, which extends through second connector ring 200, sleeve 202 and tubular extension 148. Backfilling continues until the adhesive 35 is visible within the lumen of sealing ring/strain relief member 212, distal to tubular extension 204. This seals the lead, provides additional electrical insulation, and 133 2~4 66742-305 -:, internally bonds the components together for added mechanical strength.
A second sealing ring member 214 is applied exterior to first connector ring 122. Because sleeve 126 extends through bores 123, sealing ring member 214 may be bonded directly to sleeve 126, using a suitable adhesive.
Surrounding sealing ring strain relief member 214 is a locking sleeve 218, which is intended to be used in conjunction with a deflectable beam locking member on the connector housing into which the lead is inserted. ~
Connector rin~s 122 and 200, connector pin 124, ;
tubular extensions 148 and 204 and crimp sleeve 142 may all be fabricated of an inert, biocompatible metal such as stainless -~
steel. Sleeves 126 and 202 and sealing ring members 212 and 214 are preferably fabricated of silicone rubber. Sheaths 141 and 220 and locking sleeve 218 are preferably fabricated of polyether urethane.
By repeated duplications of the connector rings, insulating sleeves and tubular extensions, a connector assembly -having any number of linearily arranged connector rings may be produced. The particular configuration of the components allows -for Ithe use of laser or resistance welding to accomplish all metal to metal connections, leading to i~creased reliability and improved reproducibility during production. Therefore, both the method of fabrication of this connector assembly and the resultant product are believed to be a substantial improvement over :, .: 66742-305 1332~44 ~:
previous in-line connector designs. :
Figure 4 shows a sectional view of the area adja-cent the ring electrode 18, illustrated in Figure 1. In this view, the interconnection of the conductor 54 and ring elec-trode 18 is illustrated. Ring electrode 18 takes the - 7a -~'~
1332~
form of a metal cylindrical tube, having a slot 64 adjacent its distal end. The stripped end of conductor 54 is laser welded to the end of slot 64 in electrode 18 at 66. This provides the electrical connection between the 5 conductor and the ring electrode. The mechanical connection between the various parts of the electrode is provided by means of a plastic sleeve 66, which is preferably fabricated of Pellethane0 2363-80A polyether urethane. Pellethane~ 2363-55D polyether urethane may 10 also be used.
The ring electrode 18 is accomplished by first sliding sleeve 66 over the multifilar coil 34. Conductor , 54 is brought out through a hole in sleeve 66. Then the assembly of coil 34 and sleeve 66 is inserted into a 15 cylindrical mold having a diameter slightly less than the inner diameter of the ring electrode 18. Heat is applied, causing the insulative sleeve to heat bond to multifilar coil 34. This also causes sleeve 66 to flow between the conductors of multifilar coil 34, stabilizing it in the 20 area of the electrode. Ring electrode 18 is slid over sleeve 66, and the stripped end of conductor 54 is laser welded to ring electrode 18 at 69. At the ends of sleeve 66, medical adhesive 68 and 70 is provided, bonding the ~ ;
insulative sleeve 66 to the multifilar coil 34 and to the 25 liner 62. This structure provides mechanical integrity to the assembly and acts as a strain relief. Insulative sheaths 14 and 20 are then slid over the ends of ;
insulating sleeve 66, and the assembly is inserted into a cylindrical mold having a diameter corresponding to the 30 outer diameter of ring electrode 18. Heat is applied, causing insulative sleeve 66 to heat bond to ring electrode 18 and to insulative sleeves 14 and 20. The resultant structure provides a lead having a uniform outer diameter in the vicinity of the ring electrode. The 35 bonding of sleeve 66 to sheaths 14 and 20 provides a continuous electrically insulative and fluid tight tube ~ ' ~,~
:' g i33~
which extends the length of the lead. During heating, sleeve 65 also collapses around conductor 54, sealing this potential point of fluid entry as well. Slot 64 in ring electrode 18 is filled with medical adhesive 70, to S complete the assembly. In order to improve the mechanical interconnection of the components of the lead, the Tefzel~9 plastic insulation of the multiconductor coil 34 and Teflon~ plastic tubing 62 are treated with Chemgrip or by glow discharge (plasma) to activate their surfaces to 10 enhance adhesion to the sleeve 66 and to silicone medical adhesive 70. A polyurethane glue, comprised of Pellethane0 2363-75D in N,N-dimethyl acetamide, is applied to the sleeve 66 and subsequently air dried to ehance adhesion to silicone medical adhesive. Adhesion 15 promoters, such as Dow Corning~ Z-6020 silane (amino alkyl functional silane), may be applied to metal or plastic components prior to the application of medical adhesive to further improve the mechanical interconnection of the lead components.
The resulting assembly provides a structure which is tightly sealed against fluid entry, and which displays a high tensile strength through the area of the ring electrode. This structure also provides a gradual transition in flexibility from the ring electrode 18 25 proximally and distally, through the combination of sleeve 66 and adhesive 68 and 70. In addition, the structure allows for the fabrication of a substantially smaller diameter ring electrode than possible using assemblies ;
which require crimping or swaging cores, as disclosed in U.S. Patent No. 4,328,812, issued to Ufford et al, discussed above.
Although the particular embodiment disclosed in this application takes the form of a cardiac pacing lead, the - ~
inventions disclosed herein are believed equally ~-35 applicable to medical electrical leads in general. In conjunction with the above description, we claim:
,~
. , . . , .. . , . . , . . . . ,, . ..... . .. .. . .. . . ... . . , . ~ .. .. . . .. . . . .
Claims (6)
1. A ring electrode assembly for use in a medical electrical lead, comprising:
an elongated coiled conductor;
an elongated, insulative sleeve having a proximal end and a distal end, said sleeve bonded to and conforming to the outer surface of said conductor coil;
a cylindrical electrode ring mounted coaxially about said insulative sleeve, such that the proximal and distal ends of said insulative sleeve extend from said cylindrical electrode, said cylindrical electrode electrically coupled to said conductor coil, said cylindrical electrode bonded to the outer surface of said insulative sleeve;
first insulative sheath extending proximally from said cylindrical electrode, said first insulative sheath bonded to and surrounding the exterior of said proximal end of said insulative sleeve; and second insulative sheath extending distally from said cylindrical electrode, said second insulative sheath bonded to and surrounding the distal end of said insulative sleeve.
an elongated coiled conductor;
an elongated, insulative sleeve having a proximal end and a distal end, said sleeve bonded to and conforming to the outer surface of said conductor coil;
a cylindrical electrode ring mounted coaxially about said insulative sleeve, such that the proximal and distal ends of said insulative sleeve extend from said cylindrical electrode, said cylindrical electrode electrically coupled to said conductor coil, said cylindrical electrode bonded to the outer surface of said insulative sleeve;
first insulative sheath extending proximally from said cylindrical electrode, said first insulative sheath bonded to and surrounding the exterior of said proximal end of said insulative sleeve; and second insulative sheath extending distally from said cylindrical electrode, said second insulative sheath bonded to and surrounding the distal end of said insulative sleeve.
2. An electrode assembly according to claim 1 wherein said conductor comprises a multipolar, multifilar coil, extending through said insulative sleeve such that a plurality of conductors extend from the proximal end of said sleeve, at least one of said conductors within said multipolar coil terminating at and coupled to said cylindrical electrode, at least a second one of said plurality of conductors in said multipolar coil extending distally from said insulative sleeve; and wherein said electrode assembly further comprises strain reliefs mounted at proximal and distal ends of said insulative sleeve, coupled to said insulative sleeve and to said multipolar coil.
3. An electrode assembly according to claim 2 further comprising an elongated tubular liner located within said multipolar, multifilar coil, said multipolar liner also coupled to said strain reliefs at said proximal and distal ends of said insulative sleeve.
4. A method for fabricating an electrode for a medical electrical lead, comprising the steps of:
selecting a multifilar coil having at least two conductors and terminating one of the conductors intermediate the ends of the coil;
selecting a generally cylindrical sleeve of a thermoplastic material, having an internal lumen and a bore perpendicular to the internal lumen and sliding said sleeve over said multifilar coil and bringing the end of said terminated conductor out through said bore;
placing said sleeve and coil into a mold and applying heat, causing said sleeve to bond to said multifilar coil and to flow between the conductors of said multifilar coil;
sliding a cylindrical ring electrode over said sleeve intermediate the proximal and distal ends of said sleeve and electrically coupling said end of said terminated conductor to said cylindrical electrode; and sliding first and second insulative sheaths over the proximal and distal ends of said sleeve, respectively, placing said ring electrode and the ends of said first and second sleeves into a mold and applying heat to bond said sleeve to said electrode and to said first and second sheaths.
selecting a multifilar coil having at least two conductors and terminating one of the conductors intermediate the ends of the coil;
selecting a generally cylindrical sleeve of a thermoplastic material, having an internal lumen and a bore perpendicular to the internal lumen and sliding said sleeve over said multifilar coil and bringing the end of said terminated conductor out through said bore;
placing said sleeve and coil into a mold and applying heat, causing said sleeve to bond to said multifilar coil and to flow between the conductors of said multifilar coil;
sliding a cylindrical ring electrode over said sleeve intermediate the proximal and distal ends of said sleeve and electrically coupling said end of said terminated conductor to said cylindrical electrode; and sliding first and second insulative sheaths over the proximal and distal ends of said sleeve, respectively, placing said ring electrode and the ends of said first and second sleeves into a mold and applying heat to bond said sleeve to said electrode and to said first and second sheaths.
5. A method according to claim 4 further comprising the step of applying adhesion enhancers to said sleeve.
6. A method according to claim 4 wherein said step of coupling said end of said terminated conductor to said electrode comprises laser welding said conductor to said electrode.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US07/198,539 US4944088A (en) | 1988-05-25 | 1988-05-25 | Ring electrode for multiconductor pacing leads |
| US07/198,539 | 1988-05-25 |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1332444C true CA1332444C (en) | 1994-10-11 |
Family
ID=22733802
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA000600478A Expired - Fee Related CA1332444C (en) | 1988-05-25 | 1989-05-24 | Ring electrode for multiconductor pacing leads |
Country Status (2)
| Country | Link |
|---|---|
| US (1) | US4944088A (en) |
| CA (1) | CA1332444C (en) |
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Also Published As
| Publication number | Publication date |
|---|---|
| US4944088A (en) | 1990-07-31 |
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