CA1204826A - Cardiac pacing lead with biodegradable fixation means - Google Patents
Cardiac pacing lead with biodegradable fixation meansInfo
- Publication number
- CA1204826A CA1204826A CA000422971A CA422971A CA1204826A CA 1204826 A CA1204826 A CA 1204826A CA 000422971 A CA000422971 A CA 000422971A CA 422971 A CA422971 A CA 422971A CA 1204826 A CA1204826 A CA 1204826A
- Authority
- CA
- Canada
- Prior art keywords
- lead
- electrode
- tissue
- fixation means
- biodegradable
- 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
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- Electrotherapy Devices (AREA)
Abstract
CARDIAC PACING LEAD WITH
BIODEGRADABLE FIXATION MEANS
ABSTRACT
Disclosed is a cardiac pacing lead comprising an electrical stimulating member (electrode) with a plurality of biodegradable fins adjacent to its tip and with or without a porous metal coating. After surgical introduction, temporary fixation of the device to the surface of the cardiac wall is supplied by the fins. The device achieves permanent fixation by ingrowth of viable tissue into the interstices of the porous electrode and/or by tissue ensheathment of the distal portion of the lead. The process of permanent fixation occurs over a period of weeks during which time the fins are gradually absorbed into the blood and/or adjacent tissue. The lead can also be used to stimulate tissue other than cardiac tissue, such as nervous system tissue.
BIODEGRADABLE FIXATION MEANS
ABSTRACT
Disclosed is a cardiac pacing lead comprising an electrical stimulating member (electrode) with a plurality of biodegradable fins adjacent to its tip and with or without a porous metal coating. After surgical introduction, temporary fixation of the device to the surface of the cardiac wall is supplied by the fins. The device achieves permanent fixation by ingrowth of viable tissue into the interstices of the porous electrode and/or by tissue ensheathment of the distal portion of the lead. The process of permanent fixation occurs over a period of weeks during which time the fins are gradually absorbed into the blood and/or adjacent tissue. The lead can also be used to stimulate tissue other than cardiac tissue, such as nervous system tissue.
Description
BACKGROUND OF THE INVENTION
Electrical monitoring and stimula~ion of heart action is well known and has been employed to counter a variety of heart dysfunctions. Such monitoring and stimulation requires a reliable means of attaching and maintaining proximity of a con-ducting electrode to the hea~t wall. This need arises, for example, in securing a pervenous cardiac pacing lead to the inside wall of the right ventricle. There have been many attemptS to achieve such a means. One way is by bonding the electrode to the endocardium with an adhesive. The problem with such adhesive bonding is that it may not provide reliable anchoring of the stimulation electrode and may produce an adverse tissue reaction. Another way is by u~e of a Rmooth-surfaced harpoon-like device. Here, a temporary anchor i8 achieved by piercing the heart wall with an absorbable "harpoon" stored within the electrode.
A third way of attaching an electrode to the inner heart wall is by the use of a tined device. Here, the electrode is held in proximity to the wall of the heart by inert tines which extend from the lead adjacent to the electrode and form an acute angle with the electrode body. TheYe tines maintain the electrode in electrical contact with the heart tissue. The problem with this type of tined device is that over time, the tines will stimulate fibrotic tissue growth which will make later removal of the lead more difficult and which may interfere with the pacing threshold as the tines are typically quite close to the electrode's contact point. Additionally, even after the for~
mation of fibrosis around the electrode, the mechanical stresses
Electrical monitoring and stimula~ion of heart action is well known and has been employed to counter a variety of heart dysfunctions. Such monitoring and stimulation requires a reliable means of attaching and maintaining proximity of a con-ducting electrode to the hea~t wall. This need arises, for example, in securing a pervenous cardiac pacing lead to the inside wall of the right ventricle. There have been many attemptS to achieve such a means. One way is by bonding the electrode to the endocardium with an adhesive. The problem with such adhesive bonding is that it may not provide reliable anchoring of the stimulation electrode and may produce an adverse tissue reaction. Another way is by u~e of a Rmooth-surfaced harpoon-like device. Here, a temporary anchor i8 achieved by piercing the heart wall with an absorbable "harpoon" stored within the electrode.
A third way of attaching an electrode to the inner heart wall is by the use of a tined device. Here, the electrode is held in proximity to the wall of the heart by inert tines which extend from the lead adjacent to the electrode and form an acute angle with the electrode body. TheYe tines maintain the electrode in electrical contact with the heart tissue. The problem with this type of tined device is that over time, the tines will stimulate fibrotic tissue growth which will make later removal of the lead more difficult and which may interfere with the pacing threshold as the tines are typically quite close to the electrode's contact point. Additionally, even after the for~
mation of fibrosis around the electrode, the mechanical stresses
-2- ~ ' i . .
_ _ _ .. . .. _ . . . .
'6 on the tines, due to myocardial con~rac~ions, can cause shifts in the electrode's position and/or additional tissue reaction.
U.S. Patent No. 4,281,669 provides novel cardiovaseular devices or implants (including pacemaker electrodes) which have biocompatibility and hence reduce thrombogenic problems. The pacemaXer electrode embodiment is preferably in the form of a rigid, porous metal coating on a dense coherent metal substrate with a network of interconnected pores substantially uniformly distributed throuyhout the coating. The rigid nature of the metal coating, the strength of the substrate-co~ ing interace and the strength of the particle-particle bond in the coating provide excellent strength and wear resistance characte~ristics.
The formation of a thin, smooth, firmly attached tissue coating on the porous surface allows the electrode to be incorporated into the cardiovascular system. This tissue coating is formed by a combination of colonization by nucleated cells circulating in the blood stream onto the porous surface and subsequent differentiation into other cell types plus true soft tissue ingrowth into the porous surface from adjacent body tissue thereby achieving a more secure attachment than has previously been the case.
Although the porous pacing electrode offers the advan-tage of improved blood tissue compatibility over a smooth pacing electrode, both require a period of sever~l weeks to months to become firmly attached, during which time another means of attaching the lead to the heart wall is needed~
SUMMARY OF THE INVENTION
The problems of the prior art are overcome by the present invention, which provides a non-penetrating means for temporary attachment of a tissue stimulating lead to the surface of the tissue to be stimulated, said means being constituted of biodegradable material absorbable in the blood and adjacent tissue of the patient.
In a preferred form, the electrical stimulating member of a cardiac pacing lead has an adherent porous metal coating. The porous metal coating comprises metal particles joined to adjacent particles to define a plurallty of connected interstitial pores uniformly distributed throughout the coating. A plurality of biodegradable fins adjacent to the electrode tip is the means for temporary attachment of the pacer lead to the surface of the heart.
After surgical introduction, temporary fixation of the device is supplied by the fins. The device achieves perman-ent fixation by lngrowth of viable tissue into the inter-stices of the porous electrode. Such growth ls blood and tissue compatible and involves very little scarring or fibrous tissue reaction. The process of permanent fixation occurs over a period of weeks during which time the flns are gradually absorbed into the blood and tissue, resul-ting in little, if any, fibrotic growth in the region of the electrode.
Various aspects of the invention are as follows:
A tissue stimulating lead comprising:
a) an electrode for establishing electrical contact with tissue to be stimulated, said elec-trode being in electrical contact with means for carrying electrical current -to the electrode, a non-conducting sheath housing the means for carrying the electrical current and 2~
b) non-tissue penetratirlg biodegradable ~ixation means for temporary attachment of the lead to the surface of the tissue to be stimulated.
A tissue stimulating lead comprising:
a) an electrode incorporated into the lead for establishing electrical contact with the tissue surface to be stimulated;
b) a coating of porous metal on the surface of the electrode; and c) biodegradable fixation means for temporary attachment of the lead to the surface of the tissue to be stimulated.
BRIEF DESCRIPTION OF THE DRAWINGS
Fig. 1 is a diagrammatic view of a heart with parts broken away showing a ventricular pacing lead and an atrial pacing lead at implant;
- 4a --~o~
Fig. 2 is a diagran~atic view of a heart with parts broken away showing a ventricular lead and an atrial lead in ' their chronic state, Fig. 3 is a side view of a distal lead assembly embodying the invention;
Fig. 4 is an end view of a distal lead assembly embodying the invention;
Fig. 5 is a sectional view of a distal lead assembly embodying the invention;
I
Fig. 6 is a cross sectional view taken across section line 6 of Fiy. 5; and, Fig. 7 is a cross sectional view taken along section line 7 of Fig. 6.
DESCRIPTION OF PREFERRED EM~ODIMENT
Fig. 1 is a diagrammatic view of the heart with parts broken away showing the atrial and ventricular leads at implant, with the porous electrode tips 16 in contact with the heart wall, the fins 18 ensnared in the trabeculi 20. Fig. 2 shows the chronic position of the leads after the fins have dissolved, the porous tips securing the leads, by a thin layer of fibrous tissue 22, which occurs within several weeks. A-~ the porous electrode tip is "seen" by the heart as "friendly" and compatible, the resultant tissue growth minimizes the adverse reactions asso ciated with the prior art. Thus, minimal tissue scarring and fibrous growth takes place to interfere with electrical transmission or to make subsequent removal difficult.
_~_ Referring now to Figs. 3-7, a preferred embodiment of the present invention, there is shown a fin member comprising fins 40 and cylindrical supporting portion S0.
Absorbable non-conducting, pliable rearwardly-projecting fins 40 are situated in close proximity to the electrode tip, so as to enable them to temporarily hold the lead in place, yet not interfere with the growth of tissue at the tip. The actual temporary fixation means may be single or multiple and is not necessarily restricted to fins but could lnclude other designs such as tines, barbs, hooks, staples, sutures, balloons and helical coils.
Materials used for the fin member are similar or identical to those used for absorbable sutures in routine use in surgery, such as treated cat gut. The preferred material for the fin member is a copolymer of "Vicryl" (trade mark), a known suture material made by Ethicon consisting of a copolymer of glycolic and lactic acid, and polycaprolactone.
Copolymerization with polycaprolactone serves to slow down degradation and to enhance flexibility.
The ins 40 are to be tapered and of ribbed design so that absorption occurs from their trailing edge tips inward toward the supporting portion 50 and forward toward the tip 30 so that loose pieces will not break off. The span of the fins will be small enough that, together with their pliable construction and tapered design, they will not interfere with implantation.
The metal electrode has a bulbou~ rounded tip 30 of "Elgiloy" ~trade mark), which is a m~tal alloy made by Elgiloy Company, and an aElgiloy~ shank portion.
The conducting tip 30 may be smooth or have a porous caating on its surface 30a, which coating consists of a ~L2~ >ti layer of sintered "Elgiloy" beads. An alternate electrode material is platln~l-iridium~ Carbon can also be used as an electrode material, although metal is the preferred electrode material.
The resilient insulating sleeve ~0 stretches over the coil and is positioned inside the electrode 30. The sleeve 90 serves to strengthen the joint and acts as a strain relief to protect the joint. The sleeve 90 is preferably made from a polyurethane, such as Pelethane~, but can be made from other materials such as silicone.
A flexible non-conducting polyurethane sheath 60 houses the "~lgiloy" coil 70 through which the stylet is inserted in the conventional manner. The sheath 60 extends over the leng~h of the pacing lead. The sheath is e~panded over the full length of the shanX portion of the electrode and bonded in place. The sheath is then coated with a cyanoacrylate adhesive, superbonder 410 from Loctite Corp. The compression molded fin member is then ¦
slipped over the electrode into its place behind the tip of the electrode. An alternate approach is to stick the end of the electrode into a mold and mold the fins right onto it at that time. An alternate material for the sheath 60 is silicone rubber. Alternate materials for the coil 70 are other metal alloys and carbon.
', The coil 70 has inside of it a metal staking pin 80 in ! order to crimp the shank around the coil without crushing the ,¦ coil. The coil is inserted into the end of the electrode and the electrode is then crimped over the stlking pin.
.
L20~ 6 The coil 70 is in electrical conduct with the electrode I
tip 30. The electrical current flows from the pacer, typically implanted in the shoulder region (not shown) via the coil 70 to the tip 30.
The lead of this invention which has been described in reference to pacemaker applications is equally effective as a tissue stimulation lead for other stimulations within the body, such as stimulation of the central or peripheral nervous system.
While this invention has been described with reference to its preferred ernbodiment, other embodiments can achieve the same result. Variations and modifications of the present inven- ¦
tion will be obvious to those skilled in the art and it is intended to cover in the appended claims all such modifications and equivalents as fall within the time spiral and scope of this invention.
I claim:
_ _ _ .. . .. _ . . . .
'6 on the tines, due to myocardial con~rac~ions, can cause shifts in the electrode's position and/or additional tissue reaction.
U.S. Patent No. 4,281,669 provides novel cardiovaseular devices or implants (including pacemaker electrodes) which have biocompatibility and hence reduce thrombogenic problems. The pacemaXer electrode embodiment is preferably in the form of a rigid, porous metal coating on a dense coherent metal substrate with a network of interconnected pores substantially uniformly distributed throuyhout the coating. The rigid nature of the metal coating, the strength of the substrate-co~ ing interace and the strength of the particle-particle bond in the coating provide excellent strength and wear resistance characte~ristics.
The formation of a thin, smooth, firmly attached tissue coating on the porous surface allows the electrode to be incorporated into the cardiovascular system. This tissue coating is formed by a combination of colonization by nucleated cells circulating in the blood stream onto the porous surface and subsequent differentiation into other cell types plus true soft tissue ingrowth into the porous surface from adjacent body tissue thereby achieving a more secure attachment than has previously been the case.
Although the porous pacing electrode offers the advan-tage of improved blood tissue compatibility over a smooth pacing electrode, both require a period of sever~l weeks to months to become firmly attached, during which time another means of attaching the lead to the heart wall is needed~
SUMMARY OF THE INVENTION
The problems of the prior art are overcome by the present invention, which provides a non-penetrating means for temporary attachment of a tissue stimulating lead to the surface of the tissue to be stimulated, said means being constituted of biodegradable material absorbable in the blood and adjacent tissue of the patient.
In a preferred form, the electrical stimulating member of a cardiac pacing lead has an adherent porous metal coating. The porous metal coating comprises metal particles joined to adjacent particles to define a plurallty of connected interstitial pores uniformly distributed throughout the coating. A plurality of biodegradable fins adjacent to the electrode tip is the means for temporary attachment of the pacer lead to the surface of the heart.
After surgical introduction, temporary fixation of the device is supplied by the fins. The device achieves perman-ent fixation by lngrowth of viable tissue into the inter-stices of the porous electrode. Such growth ls blood and tissue compatible and involves very little scarring or fibrous tissue reaction. The process of permanent fixation occurs over a period of weeks during which time the flns are gradually absorbed into the blood and tissue, resul-ting in little, if any, fibrotic growth in the region of the electrode.
Various aspects of the invention are as follows:
A tissue stimulating lead comprising:
a) an electrode for establishing electrical contact with tissue to be stimulated, said elec-trode being in electrical contact with means for carrying electrical current -to the electrode, a non-conducting sheath housing the means for carrying the electrical current and 2~
b) non-tissue penetratirlg biodegradable ~ixation means for temporary attachment of the lead to the surface of the tissue to be stimulated.
A tissue stimulating lead comprising:
a) an electrode incorporated into the lead for establishing electrical contact with the tissue surface to be stimulated;
b) a coating of porous metal on the surface of the electrode; and c) biodegradable fixation means for temporary attachment of the lead to the surface of the tissue to be stimulated.
BRIEF DESCRIPTION OF THE DRAWINGS
Fig. 1 is a diagrammatic view of a heart with parts broken away showing a ventricular pacing lead and an atrial pacing lead at implant;
- 4a --~o~
Fig. 2 is a diagran~atic view of a heart with parts broken away showing a ventricular lead and an atrial lead in ' their chronic state, Fig. 3 is a side view of a distal lead assembly embodying the invention;
Fig. 4 is an end view of a distal lead assembly embodying the invention;
Fig. 5 is a sectional view of a distal lead assembly embodying the invention;
I
Fig. 6 is a cross sectional view taken across section line 6 of Fiy. 5; and, Fig. 7 is a cross sectional view taken along section line 7 of Fig. 6.
DESCRIPTION OF PREFERRED EM~ODIMENT
Fig. 1 is a diagrammatic view of the heart with parts broken away showing the atrial and ventricular leads at implant, with the porous electrode tips 16 in contact with the heart wall, the fins 18 ensnared in the trabeculi 20. Fig. 2 shows the chronic position of the leads after the fins have dissolved, the porous tips securing the leads, by a thin layer of fibrous tissue 22, which occurs within several weeks. A-~ the porous electrode tip is "seen" by the heart as "friendly" and compatible, the resultant tissue growth minimizes the adverse reactions asso ciated with the prior art. Thus, minimal tissue scarring and fibrous growth takes place to interfere with electrical transmission or to make subsequent removal difficult.
_~_ Referring now to Figs. 3-7, a preferred embodiment of the present invention, there is shown a fin member comprising fins 40 and cylindrical supporting portion S0.
Absorbable non-conducting, pliable rearwardly-projecting fins 40 are situated in close proximity to the electrode tip, so as to enable them to temporarily hold the lead in place, yet not interfere with the growth of tissue at the tip. The actual temporary fixation means may be single or multiple and is not necessarily restricted to fins but could lnclude other designs such as tines, barbs, hooks, staples, sutures, balloons and helical coils.
Materials used for the fin member are similar or identical to those used for absorbable sutures in routine use in surgery, such as treated cat gut. The preferred material for the fin member is a copolymer of "Vicryl" (trade mark), a known suture material made by Ethicon consisting of a copolymer of glycolic and lactic acid, and polycaprolactone.
Copolymerization with polycaprolactone serves to slow down degradation and to enhance flexibility.
The ins 40 are to be tapered and of ribbed design so that absorption occurs from their trailing edge tips inward toward the supporting portion 50 and forward toward the tip 30 so that loose pieces will not break off. The span of the fins will be small enough that, together with their pliable construction and tapered design, they will not interfere with implantation.
The metal electrode has a bulbou~ rounded tip 30 of "Elgiloy" ~trade mark), which is a m~tal alloy made by Elgiloy Company, and an aElgiloy~ shank portion.
The conducting tip 30 may be smooth or have a porous caating on its surface 30a, which coating consists of a ~L2~ >ti layer of sintered "Elgiloy" beads. An alternate electrode material is platln~l-iridium~ Carbon can also be used as an electrode material, although metal is the preferred electrode material.
The resilient insulating sleeve ~0 stretches over the coil and is positioned inside the electrode 30. The sleeve 90 serves to strengthen the joint and acts as a strain relief to protect the joint. The sleeve 90 is preferably made from a polyurethane, such as Pelethane~, but can be made from other materials such as silicone.
A flexible non-conducting polyurethane sheath 60 houses the "~lgiloy" coil 70 through which the stylet is inserted in the conventional manner. The sheath 60 extends over the leng~h of the pacing lead. The sheath is e~panded over the full length of the shanX portion of the electrode and bonded in place. The sheath is then coated with a cyanoacrylate adhesive, superbonder 410 from Loctite Corp. The compression molded fin member is then ¦
slipped over the electrode into its place behind the tip of the electrode. An alternate approach is to stick the end of the electrode into a mold and mold the fins right onto it at that time. An alternate material for the sheath 60 is silicone rubber. Alternate materials for the coil 70 are other metal alloys and carbon.
', The coil 70 has inside of it a metal staking pin 80 in ! order to crimp the shank around the coil without crushing the ,¦ coil. The coil is inserted into the end of the electrode and the electrode is then crimped over the stlking pin.
.
L20~ 6 The coil 70 is in electrical conduct with the electrode I
tip 30. The electrical current flows from the pacer, typically implanted in the shoulder region (not shown) via the coil 70 to the tip 30.
The lead of this invention which has been described in reference to pacemaker applications is equally effective as a tissue stimulation lead for other stimulations within the body, such as stimulation of the central or peripheral nervous system.
While this invention has been described with reference to its preferred ernbodiment, other embodiments can achieve the same result. Variations and modifications of the present inven- ¦
tion will be obvious to those skilled in the art and it is intended to cover in the appended claims all such modifications and equivalents as fall within the time spiral and scope of this invention.
I claim:
Claims (16)
1. A tissue stimulating lead comprising:
a) an electrode for establishing electrical contact with tissue to be stimulated, said electrode being in electrical contact with means for carrying electrical current to the electrode, a non-conducting sheath housing the means for carrying the electrical current; and b) non-tissue penetrating biodegradable fixation means for temporary attachment of the lead to the surface of the tissue to be stimulated.
a) an electrode for establishing electrical contact with tissue to be stimulated, said electrode being in electrical contact with means for carrying electrical current to the electrode, a non-conducting sheath housing the means for carrying the electrical current; and b) non-tissue penetrating biodegradable fixation means for temporary attachment of the lead to the surface of the tissue to be stimulated.
2. The lead of claim 1 wherein the lead is a cardiac pacing lead.
3. The lead of claim 1 wherein the non-tissue penetrating biodegradable fixation means extends outwardly beyond the outer diameter of the lead from a location spaced rearwardly from said electrode.
4. The lead of claims 1, 2 or 3 wherein there is a coating of porous metal on the surface of the electrode.
5. The lead of claims 1, 2 or 3 wherein said biodegradable fixation means is a copolymer of a copolymer of glycolic and lactic acid and polycaprolactone.
6. The lead of claims 1, 2 or 3 wherein said biodegradable fixation means comprises a plurality of fins.
7. The lead of claims 1, 2 or 3 wherein said biodegradable fixation means is positioned on the lead in relationship to the electrode so that said means does not interfere with deposition of cellular material onto said electrode.
8. The lead of claims 1, 2 or 3 wherein said biodegradable fixation means is positioned on the lead in relationship to the electrode so that said means does not interfere with deposition of cellular material onto said electrode, and wherein said biodegradable fixation means comprises fins that are tapered to degrade from their outside edges in toward said electrode.
9. The lead of claims 1, 2 or 3, wherein said biodegradable fixation means comprises a plurality of fins, and wherein said fins are ribbed.
10. A tissue stimulating lead comprising:
a) an electrode incorporated into the lead for establishing electrical contact with the tissue surface to be stimulated;
b) a coating of porous metal on the surface of the electrode; and c) biodegradable fixation means for temporary attachment of the lead to the surface of the tissue to be stimulated.
a) an electrode incorporated into the lead for establishing electrical contact with the tissue surface to be stimulated;
b) a coating of porous metal on the surface of the electrode; and c) biodegradable fixation means for temporary attachment of the lead to the surface of the tissue to be stimulated.
11. The lead of claim 10 wherein the lead is a cardiac pacing lead.
12. The lead of claim 10 wherein the biodegradable fixation means is non-tissue penetrating.
13. The lead of claims 10, 11 or 12 wherein said biodegradable fixation means is a copolymer of a copolymer of glycolic and lactic acid and polycaprolactone.
14. The lead of claims 10, 11 or 12 wherein said biodegradable fixation means comprises a plurality of fins adjacent to the electrode tip.
15. The lead of claims 10, 11 or 12 wherein said biodegradable fixation means is positioned on the lead in relationship to the electrode so that said biodegradable fixation means does not interfere with deposition of cellular material onto said electrode.
16. The lead of claims 10, 11 or 12, wherein said biodegradable fixation means is positioned on the lead in relationship to the electrode so that said biodegradable fixation means does not interfere with deposition of cellular material onto said electrode, and wherein said biodegradable fixation means comprises fins that are tapered to degrade from their outside edges in toward said electrode.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CA000422971A CA1204826A (en) | 1983-03-07 | 1983-03-07 | Cardiac pacing lead with biodegradable fixation means |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CA000422971A CA1204826A (en) | 1983-03-07 | 1983-03-07 | Cardiac pacing lead with biodegradable fixation means |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1204826A true CA1204826A (en) | 1986-05-20 |
Family
ID=4124724
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA000422971A Expired CA1204826A (en) | 1983-03-07 | 1983-03-07 | Cardiac pacing lead with biodegradable fixation means |
Country Status (1)
| Country | Link |
|---|---|
| CA (1) | CA1204826A (en) |
-
1983
- 1983-03-07 CA CA000422971A patent/CA1204826A/en not_active Expired
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| MKEX | Expiry |