CA1081794A - Implantable transvenous pacemaker electrode - Google Patents
Implantable transvenous pacemaker electrodeInfo
- Publication number
- CA1081794A CA1081794A CA258,006A CA258006A CA1081794A CA 1081794 A CA1081794 A CA 1081794A CA 258006 A CA258006 A CA 258006A CA 1081794 A CA1081794 A CA 1081794A
- Authority
- CA
- Canada
- Prior art keywords
- conductor
- sheath
- electrode
- helix
- electrode according
- 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
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
- A61N1/057—Anchoring means; Means for fixing the head inside the heart
- A61N1/0573—Anchoring means; Means for fixing the head inside the heart chacterised by means penetrating the heart tissue, e.g. helix needle or hook
Abstract
ABSTRACT OF THE DISCLOSURE
Disclosed is a transvenously implantable electrode for a cardiac pacemaker. It comprises closely wound conductor having an end which is adapted to be located inside the heart, which end is loosely wound with a long pitch to form a helix. The helix is adapted to be screwed into the heart muscle by applying a torque to the other end of the conductor. During introduction of the electrode into the heart the helix is retained inside a protection sheath which also constitutes an insulating sheath for the flexible conductor.
Disclosed is a transvenously implantable electrode for a cardiac pacemaker. It comprises closely wound conductor having an end which is adapted to be located inside the heart, which end is loosely wound with a long pitch to form a helix. The helix is adapted to be screwed into the heart muscle by applying a torque to the other end of the conductor. During introduction of the electrode into the heart the helix is retained inside a protection sheath which also constitutes an insulating sheath for the flexible conductor.
Description
81'79'~
This invention relates to a transvenously implantable electrode for a cardiac pacemaker, the end of this electrode on the heart side being spiral-shaped for its fixation, which is achieved by screwing this spiral end into the heart muscle by means of a rotational motion applied to the other end.
Pacemaker electrodes represent the electrical link between the pulse generator and the heart tissue which is to be excited. Two methods are known for the long-lasting implantation of such electrodes: (W. Hager, A. Seling, Praxis der Schrittmachertherapie; F.K. Schattauer Verlag 1974 -Practice of pacemaker therapy; F.K. Schattauer publishers, 1974~.
1. Following thoracotomy and pericardiotomy, the electrode is sewed ~
onto the myocardium tissue, or else screwed from outside into this tissue -with the help of a special device. This technique requires relatively ; important surgery, with the corresponding risks, so that it is not always applied, particularly in the case of elderly patients.
This invention relates to a transvenously implantable electrode for a cardiac pacemaker, the end of this electrode on the heart side being spiral-shaped for its fixation, which is achieved by screwing this spiral end into the heart muscle by means of a rotational motion applied to the other end.
Pacemaker electrodes represent the electrical link between the pulse generator and the heart tissue which is to be excited. Two methods are known for the long-lasting implantation of such electrodes: (W. Hager, A. Seling, Praxis der Schrittmachertherapie; F.K. Schattauer Verlag 1974 -Practice of pacemaker therapy; F.K. Schattauer publishers, 1974~.
1. Following thoracotomy and pericardiotomy, the electrode is sewed ~
onto the myocardium tissue, or else screwed from outside into this tissue -with the help of a special device. This technique requires relatively ; important surgery, with the corresponding risks, so that it is not always applied, particularly in the case of elderly patients.
2. With the transvenous implantation method, which can also be made under local narcosis, the electrode is pushed into the heart through a vein.
Difflculties arise with this method from the tendency to a dislodging of non-fixable electrode heads as a result of heart movements and blood flow.
More particularly, when the electrode is to be fixed in the atrium, this being often desirable from the medical point of view, the risk of dislodging ~ls high, because of the smoothness of the vestibule muscles.
On account of this, it has been proposed to use other types of electrodes which are designed so as to be firmly anchored in the heart by ;~ means of ~echanlcal fixation devlces in the form of metal or plastic hooks. :
With one of these systems, the electrode carries on its end a wire ~:
countsr-hook; this requires the electrode to be pushed through a voluminous guide tube. The selection of the stlmulating location in the heart is rendered much more difficult by the stiffness of the guide tube; similarly, ~: ` ~" 1- ` :
~(~8~
pulling back the electrode is possible only with the help of the guide tube, because the wire hook is protruding.
With other hook systems, use is made of the pressure of a guiding wire (mandrel) placed inside the electrode, to drive and to push into the heart tissue a hook device which must be retracted during the introduction phase. Various embodiments of this system are using either nylon brushes or small steel hooks, but these have no real "counter-hook" effect. A secure firm hooking is achievable with all these systems only when the electrode head lies perpendicular to the tissue. If electrodes of this type come to rest at an acute angle, it can happen that only one of the hooks will grip9 and that the electrode will be dislodged by forces oriented in a correspond-ing direction, such as may result from blood flow or heart motions.
When such electrodes have to be withdrawn from the heart, the hook device must be pulled back with a nylon thread, according to one system, or else, with another type of electrode, the electrodes are pulled back together with the released hooks. It is therefore an objective for the electrode according to the present invention to be easily implanted through a vein and without requiring an auxiliary device. It should above all, to meet the requirements of an optimal electrotherapy of the heart, provide for a reliable fixation in the smooth wall of the vestibule. If the need should arise, dur-ing the implantation, to place the electrode in a location other than the one found at first, the electrode according to the invention should then be ~ released easily after its fixation, so as to be shifted to another location.
;~ According to the invention, there is provided a transvenously ~ implantable electrocLe for a cardiac pacemaker, comprising a helically-wound ; flexible conductor including a first portion which is closely wound and a -loosely wound end portion which is adapted to be located inside the heart, said conductor being contalned within a protective sheath having means adapted to cooperate with said~helically-wound conductor upon rotation thereof to cause said end portion to extend from said sheath.
; In this manner, operating like a flexible transmission shaft, the inner member, preferably, of the coaxial-shaped electrode is twisted against b 2 , . : . . :. . . . . .
79~
the outer member.
Accordin~ to a preferred embodiment of the invention, the electrical conductor is constituted by the closely wound conductor which is placed inside an insulating flexible tube.
According to a further embodiment of the invention, an element lo-cated in the electrode head operates for driving the helix part of the elec-trode out of a protection sheath, or to retract it inside it, according to the sense of rotation. Through a mechanical limitation of the rotation angle and/or through markings identifiable by X-rays, which show clearly the posi-tions of the protection sheath and of the helix, respectively to each other, it is ensured that the helix is screwed into the tissue only to the provided extent (about 2-4 mm).
The structure according to the invention has a number of important advantages: the helical shape of the electrode tip provides for a reliable fixation in the heart tissue; its removal is only possible by unscrewing it.
A repeated fixation attempt can be made immediately after unscrewing, without - having to pull back the electrode from inside the heart. After fixation, forces from practically any direction can apply to the electrode head, with-out the electrode becoming dislodged.
The lnsertion of the electrodes, the diameter of which is not different from that of non-fixable electrodes, requires no guide tube. The fixation operation does not require a guide wire (mandrel) which would impair the flexibility of the device; the angle at which the electrode should come to rest against the tissue is to a large extent without any influence and :
there is no need to take care of securing an anchoring of small hooks on all sides.
The invention will be further described while referring to the appended drawings, Figures 1, 2 and 3, which are cross-sectional views of preferred embodiments. ;
~ In all three Figures, the helix (3) is shown in its retracted position. Figure 1 represents an axial cross-section of the electrode head, with the helix (3) lying inside the protection tube (2). Pre~erably, an .
~ -3-. .
~17~
electrode of this type is designed in such manner that the inner conductor (1) serving simultaneously as electrical conductor is formed of helically ~losely wound wire, and that at its end (3) inserted in the heart, it is coiled loosely on about 10 mm length, that is with a longer winding pitch.
The external sheath of the electrode consists preferably of a flexible tube (2) made of insulating material, inside which the inner conductor (1) can be easily rotated. The insulating tube (2) serves simultaneously as an electrode head and as a protective sheath for the loosely wound portion (3) of the electrode, which must not cause any lesions during the introduction phase through the veins and heart valves. Preferably, the forward end of the helix (3) is ground so as to form a sharp point. The insulating tube com-prises also, at the electrode head, the device (5) which causes the helix to be driven axially when the internal conductor is rotated. This effect can be achieved for instance, as shown in Figure 19 by forming this device (5) as a cylinder of silicone rubber provided with grooves in which the wider portlon of the helix (3) can easily rotate.
Figure 2 shows another embodiment of the electrode head, seen in ;
longitudinal cross-section. The conversion of the rotary motion into an axial motion is obtained here by means of a plastic rod (6) which i9 helically wound with the same pitch as the portion (3) of the coiled inner conductor.
This plastic rod (6) is inserted inside the insulating tube (2) to which its ends are welded, forming small butts (8) which hold it in place and prevent its sliding out.
.
A ring (4), preferably metallic, is attached to the end of tube t2) by~means of a silicone sheath (7). This ring (shown only in ~igure 1) serves ' ' ~ .,' ~, .
.
'. ';
''' ~ :."' .. . .
l~i7g~
in both embodiments of Figure 1 and Figure 2, to ascertain by X-ray examin-ation, how far the portion (3) of the inner conductor (1) has been screwed beyond the protection sheath. The outer cover (7) serves further, in the embodiment of Figure 2, to mask the butts (8) so as to prevent the formation of a thrombosis.
Figure 3 shows a further preferred embodiment of the electrode head, also in longitudinal cross-section. Here is again shown the inner conductor (1) which simultaneously provides the electrical connection from the pulse generator to the electrode head. The forward end of this conductor is again wound with a long pitch, so as to allow it to be screwed into the tissue. As an additional feature, the diameter of the helix ~3) can be increased, as well as that of an external helix (9) at the distal end of the . .
electrode. The axial motion is achieved by bringing the inner conductor (1) in sliding contact over a certain length with an external conductor (9) ` which is similarly closely wound into an helix having a larger diameter than conductor (1), so that a screwing effect is made possible. At the front end ~` of the electrode head, the external helix (9) terminates into a ring (10) :1 .
~ which is not insulated by the silicone cover (2), so that the tissue may -: :
already be stimulated through this ring before the helix (3) is screwed lnto the tissue.
In order to keep as small as possible, in each embodiment of the invention, the area df conductive material contacting tissues, the invention further provides covering with an insulating layer, preferably of silicone rubber, those surfaces of the helically wound portion (3) of the electrode head which are not needed for the electrical stimulation.
.
,~, .
~ ~ ' .
..
., ~ .
:. .
.:: i ~ ~ -5-.~, . ..
Difflculties arise with this method from the tendency to a dislodging of non-fixable electrode heads as a result of heart movements and blood flow.
More particularly, when the electrode is to be fixed in the atrium, this being often desirable from the medical point of view, the risk of dislodging ~ls high, because of the smoothness of the vestibule muscles.
On account of this, it has been proposed to use other types of electrodes which are designed so as to be firmly anchored in the heart by ;~ means of ~echanlcal fixation devlces in the form of metal or plastic hooks. :
With one of these systems, the electrode carries on its end a wire ~:
countsr-hook; this requires the electrode to be pushed through a voluminous guide tube. The selection of the stlmulating location in the heart is rendered much more difficult by the stiffness of the guide tube; similarly, ~: ` ~" 1- ` :
~(~8~
pulling back the electrode is possible only with the help of the guide tube, because the wire hook is protruding.
With other hook systems, use is made of the pressure of a guiding wire (mandrel) placed inside the electrode, to drive and to push into the heart tissue a hook device which must be retracted during the introduction phase. Various embodiments of this system are using either nylon brushes or small steel hooks, but these have no real "counter-hook" effect. A secure firm hooking is achievable with all these systems only when the electrode head lies perpendicular to the tissue. If electrodes of this type come to rest at an acute angle, it can happen that only one of the hooks will grip9 and that the electrode will be dislodged by forces oriented in a correspond-ing direction, such as may result from blood flow or heart motions.
When such electrodes have to be withdrawn from the heart, the hook device must be pulled back with a nylon thread, according to one system, or else, with another type of electrode, the electrodes are pulled back together with the released hooks. It is therefore an objective for the electrode according to the present invention to be easily implanted through a vein and without requiring an auxiliary device. It should above all, to meet the requirements of an optimal electrotherapy of the heart, provide for a reliable fixation in the smooth wall of the vestibule. If the need should arise, dur-ing the implantation, to place the electrode in a location other than the one found at first, the electrode according to the invention should then be ~ released easily after its fixation, so as to be shifted to another location.
;~ According to the invention, there is provided a transvenously ~ implantable electrocLe for a cardiac pacemaker, comprising a helically-wound ; flexible conductor including a first portion which is closely wound and a -loosely wound end portion which is adapted to be located inside the heart, said conductor being contalned within a protective sheath having means adapted to cooperate with said~helically-wound conductor upon rotation thereof to cause said end portion to extend from said sheath.
; In this manner, operating like a flexible transmission shaft, the inner member, preferably, of the coaxial-shaped electrode is twisted against b 2 , . : . . :. . . . . .
79~
the outer member.
Accordin~ to a preferred embodiment of the invention, the electrical conductor is constituted by the closely wound conductor which is placed inside an insulating flexible tube.
According to a further embodiment of the invention, an element lo-cated in the electrode head operates for driving the helix part of the elec-trode out of a protection sheath, or to retract it inside it, according to the sense of rotation. Through a mechanical limitation of the rotation angle and/or through markings identifiable by X-rays, which show clearly the posi-tions of the protection sheath and of the helix, respectively to each other, it is ensured that the helix is screwed into the tissue only to the provided extent (about 2-4 mm).
The structure according to the invention has a number of important advantages: the helical shape of the electrode tip provides for a reliable fixation in the heart tissue; its removal is only possible by unscrewing it.
A repeated fixation attempt can be made immediately after unscrewing, without - having to pull back the electrode from inside the heart. After fixation, forces from practically any direction can apply to the electrode head, with-out the electrode becoming dislodged.
The lnsertion of the electrodes, the diameter of which is not different from that of non-fixable electrodes, requires no guide tube. The fixation operation does not require a guide wire (mandrel) which would impair the flexibility of the device; the angle at which the electrode should come to rest against the tissue is to a large extent without any influence and :
there is no need to take care of securing an anchoring of small hooks on all sides.
The invention will be further described while referring to the appended drawings, Figures 1, 2 and 3, which are cross-sectional views of preferred embodiments. ;
~ In all three Figures, the helix (3) is shown in its retracted position. Figure 1 represents an axial cross-section of the electrode head, with the helix (3) lying inside the protection tube (2). Pre~erably, an .
~ -3-. .
~17~
electrode of this type is designed in such manner that the inner conductor (1) serving simultaneously as electrical conductor is formed of helically ~losely wound wire, and that at its end (3) inserted in the heart, it is coiled loosely on about 10 mm length, that is with a longer winding pitch.
The external sheath of the electrode consists preferably of a flexible tube (2) made of insulating material, inside which the inner conductor (1) can be easily rotated. The insulating tube (2) serves simultaneously as an electrode head and as a protective sheath for the loosely wound portion (3) of the electrode, which must not cause any lesions during the introduction phase through the veins and heart valves. Preferably, the forward end of the helix (3) is ground so as to form a sharp point. The insulating tube com-prises also, at the electrode head, the device (5) which causes the helix to be driven axially when the internal conductor is rotated. This effect can be achieved for instance, as shown in Figure 19 by forming this device (5) as a cylinder of silicone rubber provided with grooves in which the wider portlon of the helix (3) can easily rotate.
Figure 2 shows another embodiment of the electrode head, seen in ;
longitudinal cross-section. The conversion of the rotary motion into an axial motion is obtained here by means of a plastic rod (6) which i9 helically wound with the same pitch as the portion (3) of the coiled inner conductor.
This plastic rod (6) is inserted inside the insulating tube (2) to which its ends are welded, forming small butts (8) which hold it in place and prevent its sliding out.
.
A ring (4), preferably metallic, is attached to the end of tube t2) by~means of a silicone sheath (7). This ring (shown only in ~igure 1) serves ' ' ~ .,' ~, .
.
'. ';
''' ~ :."' .. . .
l~i7g~
in both embodiments of Figure 1 and Figure 2, to ascertain by X-ray examin-ation, how far the portion (3) of the inner conductor (1) has been screwed beyond the protection sheath. The outer cover (7) serves further, in the embodiment of Figure 2, to mask the butts (8) so as to prevent the formation of a thrombosis.
Figure 3 shows a further preferred embodiment of the electrode head, also in longitudinal cross-section. Here is again shown the inner conductor (1) which simultaneously provides the electrical connection from the pulse generator to the electrode head. The forward end of this conductor is again wound with a long pitch, so as to allow it to be screwed into the tissue. As an additional feature, the diameter of the helix ~3) can be increased, as well as that of an external helix (9) at the distal end of the . .
electrode. The axial motion is achieved by bringing the inner conductor (1) in sliding contact over a certain length with an external conductor (9) ` which is similarly closely wound into an helix having a larger diameter than conductor (1), so that a screwing effect is made possible. At the front end ~` of the electrode head, the external helix (9) terminates into a ring (10) :1 .
~ which is not insulated by the silicone cover (2), so that the tissue may -: :
already be stimulated through this ring before the helix (3) is screwed lnto the tissue.
In order to keep as small as possible, in each embodiment of the invention, the area df conductive material contacting tissues, the invention further provides covering with an insulating layer, preferably of silicone rubber, those surfaces of the helically wound portion (3) of the electrode head which are not needed for the electrical stimulation.
.
,~, .
~ ~ ' .
..
., ~ .
:. .
.:: i ~ ~ -5-.~, . ..
Claims (8)
PROPERTY OR PRIVILEGE IS CLAIMED ARE DEFINED AS FOLLOWS:
1. A transvenously implantable electrode for a cardiac pacemaker, comprising a helically-wound flexible conductor including a first portion which is closely wound and a loosely wound end portion which is adapted to be located inside the heart, said conductor being contained within a pro-tective sheath having means adapted to cooperate with said helically-wound conductor upon rotation thereof to cause said end portion to extend from said sheath.
2. An electrode according to claim 1, characterized in that said sheath is formed of insulating material.
3. An electrode according to claim 2, characterized in that said means comprises a screw-like arrangement formed by grooves in a plastic block hav-ing a configuration matching the windings of the end portion of the conductor and allowing the conductor to slide easily therein.
4. An electrode according to claim 2, characterized in that said means comprises a screw-like arrangement consisting of a plastic rod inserted in a front end of the sheath with a winding pitch matching that of the end portion of the conductor, the rod extending through the sheath and having fused ends so as to form small retaining butts for preventing the rod from sliding out.
5. An electrode according to claim 2, characterized in that the axial motion is achieved by meshing of the windings of the closely wound conductor with the windings of a surrounding conductor embedded in the sheath when the closely wound conductor is rotated.
6. An electrode according to claim 5, characterized in that a metal ring protrudes at the front end of the electrode, this ring being the first winding of the externally coiled conductor which is electrically linked to the inner conductor through close contact therewith, so that a stimulation of the tissue is possible through this ring even before the helix is rotated out.
7. Pacemaker electrode according to claim 6, characterized in that a ring made of a material opaque to X-rays is placed at the front end of the protective sheath and is coated with an insulating material, so that it may be ascertained, by X-ray inspection, where are the respective locations of the helix and of the protection sheath.
8. Pacemaker electrode according to claim 1, 2 or 7, characterized in that the protective sheath is surrounded by a further wire helix similarly insulated from the heart tissue by an insulating sheath, the distal end of said outer helix being uninsulated, so that when this outer helix is connected to a pacemaker unit the patient's heart may be stimulated therethrough.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| DE19752533766 DE2533766C2 (en) | 1975-07-29 | 1975-07-29 | Implantable transvenous pacemaker lead |
| DEP2533766.0 | 1975-07-29 |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1081794A true CA1081794A (en) | 1980-07-15 |
Family
ID=5952667
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA258,006A Expired CA1081794A (en) | 1975-07-29 | 1976-07-28 | Implantable transvenous pacemaker electrode |
Country Status (8)
| Country | Link |
|---|---|
| JP (1) | JPS5231592A (en) |
| CA (1) | CA1081794A (en) |
| DE (1) | DE2533766C2 (en) |
| FR (1) | FR2319384A1 (en) |
| GB (1) | GB1560411A (en) |
| IT (1) | IT1066586B (en) |
| NL (1) | NL175883C (en) |
| SE (1) | SE427524B (en) |
Families Citing this family (13)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DE2539553A1 (en) * | 1975-09-05 | 1977-03-10 | Osypka Peter | ELECTRODE ARRANGEMENT FOR MEDICAL PURPOSES |
| US4026303A (en) | 1975-11-17 | 1977-05-31 | Vitatron Medical B.V. | Endocardial pacing electrode |
| DE2736737A1 (en) * | 1977-08-16 | 1979-03-01 | Bisping Hans Juergen | IMPLANTABLE ELECTRODE |
| US4146036A (en) * | 1977-10-06 | 1979-03-27 | Medtronic, Inc. | Body-implantable lead with protector for tissue securing means |
| US4136701A (en) * | 1977-12-09 | 1979-01-30 | Barton Steven A | Retractable stimulation electrode apparatus |
| NL8004629A (en) * | 1979-08-27 | 1981-03-03 | Medtronic Inc | ENDO-CARDIAL HEART STIMULATOR PIPE. |
| DE3020586A1 (en) * | 1980-05-30 | 1981-12-03 | Hans-Jürgen Dipl.-Ing. 5100 Aachen Bisping | IMPLANTABLE ELECTRODE PROBE |
| DE3020584A1 (en) * | 1980-05-30 | 1981-12-03 | Hans-Jürgen Dipl.-Ing. 5100 Aachen Bisping | Electrode probe for body implantation - has stop mechanism between fixing coil and guide slot in head with flexible small diameter supply line |
| DE3027383A1 (en) * | 1980-07-16 | 1982-02-04 | Biotronik Meß- und Therapiegeräte GmbH & Co Ingenieurbüro Berlin, 1000 Berlin | TRANSVENOUS CARDIAC ELECTRODE |
| US4550737A (en) * | 1983-10-12 | 1985-11-05 | Peter Osypka | Intravenously implantable electrode lead for use with cardiac pacemakers |
| EP0149431A3 (en) * | 1983-10-25 | 1987-02-04 | C.B. BIOELETTRONICA S.r.l. | Active anchored intracavitary electrocatheter with retractible spring wire |
| US7027876B2 (en) | 2001-10-12 | 2006-04-11 | Medtronic, Inc. | Lead system for providing electrical stimulation to the Bundle of His |
| DE602005022122D1 (en) * | 2005-08-22 | 2010-08-12 | St Jude Medical | TOOL FOR FIXING A HEART STIMULATOR LINE AT A DESIRED POINT IN THE HEART |
Family Cites Families (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US2240087A (en) * | 1940-01-10 | 1941-04-29 | Barrett Engineering Company | Drive mechanism |
| FR888009A (en) * | 1942-01-24 | 1943-11-30 | Spiral tip in two parts, for support stops used in bowden sheaths or all applications | |
| US3416534A (en) * | 1966-04-11 | 1968-12-17 | Gen Electric | Body organ electrode |
| US3416533A (en) * | 1966-05-20 | 1968-12-17 | Gen Electric | Conductive catheter |
| US4000745A (en) * | 1968-08-05 | 1977-01-04 | Goldberg Edward M | Electrical leads for cardiac stimulators and related methods and means |
| NL162840C (en) * | 1970-10-08 | 1980-07-15 | Vitatron Medical N V | INTRACARDIAL ELECTRODE FOR HEART STIMULATION. |
| CH545624A (en) * | 1970-12-15 | 1974-02-15 | ||
| US3844292A (en) * | 1972-06-09 | 1974-10-29 | Medtronic Inc | Intravascular lead assembly |
| US3902501A (en) * | 1973-06-21 | 1975-09-02 | Medtronic Inc | Endocardial electrode |
| AR208018A1 (en) * | 1975-02-07 | 1976-11-22 | Medtronic Inc | A NON-FIBROUS HEART ELECTRODE |
-
1975
- 1975-07-29 DE DE19752533766 patent/DE2533766C2/en not_active Expired
-
1976
- 1976-07-21 IT IT5054576A patent/IT1066586B/en active
- 1976-07-28 CA CA258,006A patent/CA1081794A/en not_active Expired
- 1976-07-28 JP JP51090777A patent/JPS5231592A/en active Granted
- 1976-07-28 NL NL7608363A patent/NL175883C/en not_active IP Right Cessation
- 1976-07-28 SE SE7608505A patent/SE427524B/en not_active IP Right Cessation
- 1976-07-29 GB GB3172876A patent/GB1560411A/en not_active Expired
- 1976-07-29 FR FR7623218A patent/FR2319384A1/en active Granted
Also Published As
| Publication number | Publication date |
|---|---|
| DE2533766C2 (en) | 1986-01-23 |
| FR2319384B1 (en) | 1982-03-26 |
| GB1560411A (en) | 1980-02-06 |
| NL7608363A (en) | 1977-02-01 |
| SE427524B (en) | 1983-04-18 |
| DE2533766A1 (en) | 1977-02-03 |
| FR2319384A1 (en) | 1977-02-25 |
| NL175883B (en) | 1984-08-16 |
| NL175883C (en) | 1985-01-16 |
| SE7608505L (en) | 1977-01-30 |
| JPS5644756B2 (en) | 1981-10-21 |
| IT1066586B (en) | 1985-03-12 |
| JPS5231592A (en) | 1977-03-10 |
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