CA2107246C - Defibrillation patch electrode having conductor-free resilient zone for minimally invasive deployment - Google Patents
Defibrillation patch electrode having conductor-free resilient zone for minimally invasive deploymentInfo
- Publication number
- CA2107246C CA2107246C CA002107246A CA2107246A CA2107246C CA 2107246 C CA2107246 C CA 2107246C CA 002107246 A CA002107246 A CA 002107246A CA 2107246 A CA2107246 A CA 2107246A CA 2107246 C CA2107246 C CA 2107246C
- Authority
- CA
- Canada
- Prior art keywords
- electrode
- conductive elements
- conductor
- orientation
- electrically conductive
- 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
- A61N1/0587—Epicardial electrode systems; Endocardial electrodes piercing the pericardium
Abstract
A cardioversion/defibrillation electrode comprising an insulative element which supports one or more planar conductive elements. The conductive elements are spaced apart from each other by a "conductor-free" region, which serves as a spring loaded hinge about which the electrode may preferentially bend. The electrode is thereby spring loaded to adopt a substantially planar orientation in a relaxed state but is capable of bending to a non planar orientation wherein the electrode is folded about the hinge to facilitate intrathoracic introduction. After introduction, the spring loaded hinge causes the electrode to adopt its relaxed substantially planar orientation for attachment on or near the heart surface. Due to the preferential bending in the "conductor-free"
region, the electrode conductive elements are not permanently or substantially deform during implantation.
region, the electrode conductive elements are not permanently or substantially deform during implantation.
Description
2~ Q724 6 DEFIBRILLATION PATCH ELECTRODE HAVING CO~ OK-FREE
RESILIENT ZONE FOR MINIMALLY INVASIVE DEPLOYMENT
BACKGROUND OF THE INVENTION
The present invention relates to a cardioversion/defibrillation electrode, and more particularly, to a patch electrode having an improved structure to simplify implantation procedures and to preserve the structural integrity of the electrode after implantation.
In the field of cardiover-sion/defibrillation, electrodes are mounted in, on or about the heart to discharge and generate an electric field which is capable of terminating potentially lethal tachyarrhythmias. The electrodes come in vari-ous forms, including endocardial catheter electrodes, epicardial patch electrodes, and subcutaneous elec-trodes. A conventional patch electrode such as shown in U. S. Patent No. 4,291,707, Heilman et al, is designed to attach on or near the heart surface and is generally a thin planar device having a lead extending therefrom which connects electrically conductive sur-faces on the electrode with a source of electrical energy, typically embodied as an implantable pulse generator.
The patch electrode includes conductive surfaces on the side designed to face the heart. These conductive surfaces may 210724~
~ake on a variety of shapes and sizes. One type of conductive element useful on a patch electrode is a conductive mesh. The conductive mesh is attached to an insulative backing material and is connected to insulated electrically conductive leads. To adapt to the changing surfaces of the heart during cardiac contractions and to facilitate implantation into the thoracic region, some patch electrodes have been designed with a degree of flexibility.
A problem with patch electrodes heretof~re known is that during intrathoracic introduction procedures, the electrode must be bent and contorted to achieve proper placement on or about the heart. Consequently, the conductive mesh on the electrode is subject to a bending stress which may exceed the mesh material yield stress, with the result that it may become permanently deformed after the introduction procedure. The permanently deformed electrode may not function properly since the conductive mesh no longer conforms optimally to the generally curved surfaces of the epicardium.
U.S. Patent No. 5,042,463 - Lekholm et al discloses several embodiments of a flexible, planar patch electrode for defibrillation in which there are "conductor-free" zones in which the patch could be folded without deforming the electrode conduc-tor. However, in these "conductor-free" zones the insulative backing is removed, such that the electrode would not have a resilient spring-like hinge effect that would aid in returning the planar patch to its natural planar state during deployment. Thus, any folding of the planar patch electrode shown in the Lekholm et 2~ ~724 6 al patent during an implantation procedure would cause irreparable deformation and possible damage of the electrode conductor in the region of the electrode where the lead portion joins the electrode portion.
U. S. Patent No. 4,827,932, Ideker et al, illustrates a large partially bifurcated conformal mesh patch for epicardial defibrillation. However, it teaches con-tiguous mesh conductive surfaces without regard for the prevention of deformation of the mesh conductive sur-face. U. S. Patent No. 4,938,231, Milijasevic, depictsan electrode having l'conductor-freell zones, but they are in the form of radial slits and semi-circular slots that would prevent folding for improved deployment using min;m~lly invasive techniques.
SUMMARY OF THE INVENTION
It is a primary object of the present invention to provide a cardioversion/defibrillation patch electrode structure which eliminates permanent deformation of the electrode conductive surface after intrathoracic introduction procedures.
A construction in accordance with the present invention comprises a cardiover-sion/defibrillation patch electrode for insertion through a thoracoscopic port comprising an insulative element having first and second opposing surfaces, and at least two electrically conductive elements disposed on said first surface of said insulative element and separated from each other by a conductor-free region of said first surface of said insulative element, said conductor-free region defining a hinge about which the electrode is caused to bend by deformation forces encountered during implantation from a substantially planar orientation in a relaxed state to folded, springy orientation, said springy orientation causing said electrode to return to said substantially planar configuration when said deformation forces are removed.
~ ~7~4~
More specifically, the present invention relates to a cardioversion/defibrillation electrode designed for implantation on or near the heart surface.
The electrode comprises a resilient insulative element which supports one or more electrically conductive surface elements. The conductive surface elements, typically formed of a conductive mesh, are spaced apart from each other so as to form a "conductor-free" region or regions, which region or regions serve as a hinge about which the electrode may be bent. The electrode - 3a -i ~s designed to adopt a substantially planar orientation in a relaxed state but is capable of being bent in the "conductor-free"
region to a non-planar orientation wherein the electrode is folded like a hinge to facilitate intrathoracic introduction. After introduction the bent region or regions each act as a spring loaded hinge which causes the electrode to adopt its relaxed substantially planar orientation for attachment on or near the heart surface.
By providing preferential bending regions, and thus controlling the particular manner in which the electrode bends during introduction, the problem of permanent electrode mesh deformation after intrathoracic introduction is eliminated.
The above and other objects and advantages will become more readily apparent when reference is made to the following description taken in conjunction with the accompanying drawings.
BRIEF DESCRIPTION OF THE DRAWINGS
FIG. l i~ a top view of a cardioversion/defibrillation patch electrode and lead constructed in accordance with the present invention.
FIG. 2 is a side view of the electrode shown in FIG. 1.
FIG. 3 is an end view of the electrode of FIG. 1 shown in its folded, spring loaded orientation, and in its relaxed orientation by dashed lines.
FIGS. 4 and 5 are views of the electrode and lead during intrathoracic introduction procedures.
FIG. 6 is a top view oE a second embodiment of a cardioversion/defibrillation patch electrode and lead constructed in accordance with the present invention.
FIG. 7 is an end view of the electrode of FIG. 6 shown in its folded, spring loaded orientation, and in its relaxed orientation by dashed lines.
FIG. 8 is a top view of a third embodiment of a car-dioversion/defibrillation patch electrode and lead constructed in accordance with the present invention.
FIG. 9 is a bottom view of the third embodiment of a cardioversion/defibrillation patch electrode shown in FIG. 8.
FIG. 10 is a partial cross-sectional side view of the third embodiment of a cardioversion/defibrillation patch electrode shown in FIG. 8.
FIG. 11 is a top view of a fourth embodiment of a cardioversiontdefibrillation patch electrode and lead constructed in accordance with the present invention.
FIG. 12 is an end view of the fourth embodiment of the cardioversion/defibrillation patch electrode shown in FIG. 11 in its relaxed orientation.
FIG. 13 is an end view of the electrode of FIG. 11 shown in its folded, spring loaded orientation.
FIG. 14 is a perspective view of the thorax of a human body illustrating the heart and the implanted location of the cardioversion/defibrillation patch electrode of this invention.
2~072'1~
DETAILED DESCRIPTION OF THE DRAWINGS
Referring first to FIGS. 1 and 2, the cardioversion/
defibrillation electrode assembly according to the present invention is generally shown at 10 and comprises a planar conduc-5 tive electrode portion 12 and a lead member 14. The electrodeportion 12 is formed of two or more electrically conductive elements 16 and 18 attached to an electrically insulative and generally mechanically resilient backing element 20. The conduc-tive elements 16 and 18 shown as a wire mesh structure are 10 connected at nodes 26 and 28 respectively to insulated conductors 22 and 24 respectively. The connections at nodes 26 and 28 may be made by well known wire crimping or spot welding processes. The conductors 22 and 24 which are carried inside of lead member 14 are connected in common to a terminal pin 29 at the proximal end of the 15 lead member 14. As is well known in the art, the terminal pin 29 plugs into an implantable pulse generator unit (not shown) for delivery of high strength electrical shocks in the order of 0.1 to 35 Joules.
The mesh elements 16 and 18 are separated from each other 20 on the insulative backing element 20 by a "mesh-free" region 30 which in a preferred embodiment is approximately 1 to 10 mil-limeters wide. The mesh elements 16 and 18 are substantially coplanar when the backing element 20 is in its natural flat condition. The purpose of the mesh-free region 30 is to provide 25 a "spring loaded" hinge structure to the electrode portion 12 so that the electrode portion 12 may bend, as a hinge, along the 210724~
dotted line 32, in the mesh-free region 30. This is shown in FIG.
RESILIENT ZONE FOR MINIMALLY INVASIVE DEPLOYMENT
BACKGROUND OF THE INVENTION
The present invention relates to a cardioversion/defibrillation electrode, and more particularly, to a patch electrode having an improved structure to simplify implantation procedures and to preserve the structural integrity of the electrode after implantation.
In the field of cardiover-sion/defibrillation, electrodes are mounted in, on or about the heart to discharge and generate an electric field which is capable of terminating potentially lethal tachyarrhythmias. The electrodes come in vari-ous forms, including endocardial catheter electrodes, epicardial patch electrodes, and subcutaneous elec-trodes. A conventional patch electrode such as shown in U. S. Patent No. 4,291,707, Heilman et al, is designed to attach on or near the heart surface and is generally a thin planar device having a lead extending therefrom which connects electrically conductive sur-faces on the electrode with a source of electrical energy, typically embodied as an implantable pulse generator.
The patch electrode includes conductive surfaces on the side designed to face the heart. These conductive surfaces may 210724~
~ake on a variety of shapes and sizes. One type of conductive element useful on a patch electrode is a conductive mesh. The conductive mesh is attached to an insulative backing material and is connected to insulated electrically conductive leads. To adapt to the changing surfaces of the heart during cardiac contractions and to facilitate implantation into the thoracic region, some patch electrodes have been designed with a degree of flexibility.
A problem with patch electrodes heretof~re known is that during intrathoracic introduction procedures, the electrode must be bent and contorted to achieve proper placement on or about the heart. Consequently, the conductive mesh on the electrode is subject to a bending stress which may exceed the mesh material yield stress, with the result that it may become permanently deformed after the introduction procedure. The permanently deformed electrode may not function properly since the conductive mesh no longer conforms optimally to the generally curved surfaces of the epicardium.
U.S. Patent No. 5,042,463 - Lekholm et al discloses several embodiments of a flexible, planar patch electrode for defibrillation in which there are "conductor-free" zones in which the patch could be folded without deforming the electrode conduc-tor. However, in these "conductor-free" zones the insulative backing is removed, such that the electrode would not have a resilient spring-like hinge effect that would aid in returning the planar patch to its natural planar state during deployment. Thus, any folding of the planar patch electrode shown in the Lekholm et 2~ ~724 6 al patent during an implantation procedure would cause irreparable deformation and possible damage of the electrode conductor in the region of the electrode where the lead portion joins the electrode portion.
U. S. Patent No. 4,827,932, Ideker et al, illustrates a large partially bifurcated conformal mesh patch for epicardial defibrillation. However, it teaches con-tiguous mesh conductive surfaces without regard for the prevention of deformation of the mesh conductive sur-face. U. S. Patent No. 4,938,231, Milijasevic, depictsan electrode having l'conductor-freell zones, but they are in the form of radial slits and semi-circular slots that would prevent folding for improved deployment using min;m~lly invasive techniques.
SUMMARY OF THE INVENTION
It is a primary object of the present invention to provide a cardioversion/defibrillation patch electrode structure which eliminates permanent deformation of the electrode conductive surface after intrathoracic introduction procedures.
A construction in accordance with the present invention comprises a cardiover-sion/defibrillation patch electrode for insertion through a thoracoscopic port comprising an insulative element having first and second opposing surfaces, and at least two electrically conductive elements disposed on said first surface of said insulative element and separated from each other by a conductor-free region of said first surface of said insulative element, said conductor-free region defining a hinge about which the electrode is caused to bend by deformation forces encountered during implantation from a substantially planar orientation in a relaxed state to folded, springy orientation, said springy orientation causing said electrode to return to said substantially planar configuration when said deformation forces are removed.
~ ~7~4~
More specifically, the present invention relates to a cardioversion/defibrillation electrode designed for implantation on or near the heart surface.
The electrode comprises a resilient insulative element which supports one or more electrically conductive surface elements. The conductive surface elements, typically formed of a conductive mesh, are spaced apart from each other so as to form a "conductor-free" region or regions, which region or regions serve as a hinge about which the electrode may be bent. The electrode - 3a -i ~s designed to adopt a substantially planar orientation in a relaxed state but is capable of being bent in the "conductor-free"
region to a non-planar orientation wherein the electrode is folded like a hinge to facilitate intrathoracic introduction. After introduction the bent region or regions each act as a spring loaded hinge which causes the electrode to adopt its relaxed substantially planar orientation for attachment on or near the heart surface.
By providing preferential bending regions, and thus controlling the particular manner in which the electrode bends during introduction, the problem of permanent electrode mesh deformation after intrathoracic introduction is eliminated.
The above and other objects and advantages will become more readily apparent when reference is made to the following description taken in conjunction with the accompanying drawings.
BRIEF DESCRIPTION OF THE DRAWINGS
FIG. l i~ a top view of a cardioversion/defibrillation patch electrode and lead constructed in accordance with the present invention.
FIG. 2 is a side view of the electrode shown in FIG. 1.
FIG. 3 is an end view of the electrode of FIG. 1 shown in its folded, spring loaded orientation, and in its relaxed orientation by dashed lines.
FIGS. 4 and 5 are views of the electrode and lead during intrathoracic introduction procedures.
FIG. 6 is a top view oE a second embodiment of a cardioversion/defibrillation patch electrode and lead constructed in accordance with the present invention.
FIG. 7 is an end view of the electrode of FIG. 6 shown in its folded, spring loaded orientation, and in its relaxed orientation by dashed lines.
FIG. 8 is a top view of a third embodiment of a car-dioversion/defibrillation patch electrode and lead constructed in accordance with the present invention.
FIG. 9 is a bottom view of the third embodiment of a cardioversion/defibrillation patch electrode shown in FIG. 8.
FIG. 10 is a partial cross-sectional side view of the third embodiment of a cardioversion/defibrillation patch electrode shown in FIG. 8.
FIG. 11 is a top view of a fourth embodiment of a cardioversiontdefibrillation patch electrode and lead constructed in accordance with the present invention.
FIG. 12 is an end view of the fourth embodiment of the cardioversion/defibrillation patch electrode shown in FIG. 11 in its relaxed orientation.
FIG. 13 is an end view of the electrode of FIG. 11 shown in its folded, spring loaded orientation.
FIG. 14 is a perspective view of the thorax of a human body illustrating the heart and the implanted location of the cardioversion/defibrillation patch electrode of this invention.
2~072'1~
DETAILED DESCRIPTION OF THE DRAWINGS
Referring first to FIGS. 1 and 2, the cardioversion/
defibrillation electrode assembly according to the present invention is generally shown at 10 and comprises a planar conduc-5 tive electrode portion 12 and a lead member 14. The electrodeportion 12 is formed of two or more electrically conductive elements 16 and 18 attached to an electrically insulative and generally mechanically resilient backing element 20. The conduc-tive elements 16 and 18 shown as a wire mesh structure are 10 connected at nodes 26 and 28 respectively to insulated conductors 22 and 24 respectively. The connections at nodes 26 and 28 may be made by well known wire crimping or spot welding processes. The conductors 22 and 24 which are carried inside of lead member 14 are connected in common to a terminal pin 29 at the proximal end of the 15 lead member 14. As is well known in the art, the terminal pin 29 plugs into an implantable pulse generator unit (not shown) for delivery of high strength electrical shocks in the order of 0.1 to 35 Joules.
The mesh elements 16 and 18 are separated from each other 20 on the insulative backing element 20 by a "mesh-free" region 30 which in a preferred embodiment is approximately 1 to 10 mil-limeters wide. The mesh elements 16 and 18 are substantially coplanar when the backing element 20 is in its natural flat condition. The purpose of the mesh-free region 30 is to provide 25 a "spring loaded" hinge structure to the electrode portion 12 so that the electrode portion 12 may bend, as a hinge, along the 210724~
dotted line 32, in the mesh-free region 30. This is shown in FIG.
3 where the dashed lines represent the electrode portion 12 in its natural or relaxed orientation and the solid lines represent the electrode portion 12 in its folded, spring loaded orientation. Due to the nature of the insulative backing material and the position-ing of the mesh elements, the electrode portion 12 is spring loaded to adopt a planar orientation as shown in FIGS. 1 and 2. An adequate spring force in the mesh-free region~is produced by stressing the resilient material. A preferred material for the backing element is Dacron~ reinforced silicone rubber sheeting.
Because the electrode portion is designed to preferen-tially bend in the region 30, the mesh elements 16 and 18 are not bent. Therefore, there is no deformation of the mesh elements 16 and 18 when the electrode portion is folded for intrathoracic introduction.
FIGS. 4 and 5 illustrate initial and final steps of introducing the electrode 10 into the thoracic region. The electrode portion 12 is folded in the region 30 and inserted into a cannula 34 or other introducing means as shown in FIG. 4. At this point, the electrode portion is in its folded, spring loaded orientation. Once the cannula 34 is positioned near the heart surface, the electrode portion 12 is urged out of the cannula 34.
Being then free of the restraint of the cannula 34, it adopts its relaxed planar orientation as shown in FIG. 5. The mesh elements 16 and 18 adopt a substantially flat orientation to facilitate attachment on or near the heart surface.
The electrode according to the present invention may be implanted in any one of several configurations. As an example, one such electrode may be implanted on the high lateral right ventricle and two such electrodes on the left ventricle, one in an anterior and the other in a posterior position. The two left ventricle electrodes are electrically connected in common to form a common anode or cathode.
It is envisioned that the electrode be introduced through a thoracoscopic trocar or a small incision, and thereafter a cannula or other introducing means used to position the electrode on or near the heart surface. Referring to FIG. 14, the thorax 36 of a human body is show with rib cage 38 and heart 40. A pair of thoracoscopic ports 42 and 44 are shown positioned in the rib cage.
These ports, which pass through the chest wall and extend into the lS thoracic cavity, may be used for introducing and subsequent manipulating and fixing to tissue on or around the heart the patch electrode of this invention. The thoracoscopic ports 42 and 44, which typically have an internal diameter of 10 to 15 millimeters, may be placed in any of several intercostal locations, including those shown in FIG. 14. By way of introduction through the thoracoscopic ports, multiply electrically common electrodes 46 and 48 constructed in accordance with this invention are positioned on the left heart. The electrodes 46 and 48 are connected through an adaptor S0 to the negative terminal of an implantable pulse generator unit ~not shown). A single electrode 52 is shown positioned on the heart and connected to the positive terminal of 21072~
'a~ implantable pulse generator unit (not shown).
Larger patch electrodes, having a surface area in the range of 20 to 40 sq. cm. may have more than one mesh-free region so that the electrode may be folded in a "pleated" fashion to decrease the profile of the electrode for introduction.
Referring to FIGS. 6 and 7, an electrode in accordance with this invention with three substantially, parallel mesh conductors 54, 56, and 58 is shown. An electrode constructed in this manner has two parallel "conductor-free" zones. Referring to ~IG. 7, the electrode of FIG. 6 is shown in its folded or pleaded state for deployment using minimally invasive techniques. The dashed lines in FIG. 7 show the unstressed, planar shape of the electrode as it appears in use. As shown in FIG. 6, tabs 60 which extend beyond the border of the electrode portion 12 provide a convenient means of fixation to tissues for electrode immobiliza-tion. The tabs are typically formed of Dacron~ reinforced silicone rubber sheeting 0.25 to 1 millimeter thick, or a suitable porous, tissue-in-growth-promoting fabric such as Dacron~. The tabs are ~o fixed to the tissue by using staples or sutures, either solely or in combination.
While mesh type conductive elements have been illustrated and described with respect to the embodiments of the invention shown in FIGS. 1 through ~, the use of other types of conductive elements is encompassed within the invention. Conductive elements other than mesh which could be used are foils, wires or preferably 21 072~
~~ulti-filar coils (0.5 to 2.5 millimeters major diameter) which are embedded in the insulative backing.
FIG. 8 shows a electrode assembly in accordance with this invention wherein two loops 62 and 64 of multi-filar coils are located on either side of a centerline 32 of the back-ing element 20, along which the electrode assembly may be folded for implanta-tion.
As shown in FIGS. 9 and 10, the electrode assembly shown in FIG. 8 may be provided with ribs to augment the spring force of the conductor-free zone. The ribs 66 have a height of 1 to 5 times the thickness of the backing element 20 and are placed generally perpendicular to the centerline 32 of the backing element. The ribs 66 are preferably formed of silicone rubber of the same or higher durometer compared to the material of which the backing element 20 is formed and should nominally be two to ten times the backing element 20 thickness in width. The effect of the ribs 66 is to increase the spring-like return force generated by the conductor-free zone. With the use of the ribs, the electrode portion is more forcefully returned to a planar state when the deformation forces of implantation are removed.
FIG. 11 shows still another embodiment of this invention wherein three strands of multi-filar coils are located on the backing element parallel to each other. The patch electrode of FIG. 11 is shown in its relaxed or implanted orientation in FIG.
12, and in the folded or spring loaded orientation in which it is placed during an intrathoracic introduction procedure in FIG. 13.
~~ The above description is2 ~e7n~ed by way of example only and is not intended to limit the present invention in any way except as set forth in the accompanying claims.
, - . . .
Because the electrode portion is designed to preferen-tially bend in the region 30, the mesh elements 16 and 18 are not bent. Therefore, there is no deformation of the mesh elements 16 and 18 when the electrode portion is folded for intrathoracic introduction.
FIGS. 4 and 5 illustrate initial and final steps of introducing the electrode 10 into the thoracic region. The electrode portion 12 is folded in the region 30 and inserted into a cannula 34 or other introducing means as shown in FIG. 4. At this point, the electrode portion is in its folded, spring loaded orientation. Once the cannula 34 is positioned near the heart surface, the electrode portion 12 is urged out of the cannula 34.
Being then free of the restraint of the cannula 34, it adopts its relaxed planar orientation as shown in FIG. 5. The mesh elements 16 and 18 adopt a substantially flat orientation to facilitate attachment on or near the heart surface.
The electrode according to the present invention may be implanted in any one of several configurations. As an example, one such electrode may be implanted on the high lateral right ventricle and two such electrodes on the left ventricle, one in an anterior and the other in a posterior position. The two left ventricle electrodes are electrically connected in common to form a common anode or cathode.
It is envisioned that the electrode be introduced through a thoracoscopic trocar or a small incision, and thereafter a cannula or other introducing means used to position the electrode on or near the heart surface. Referring to FIG. 14, the thorax 36 of a human body is show with rib cage 38 and heart 40. A pair of thoracoscopic ports 42 and 44 are shown positioned in the rib cage.
These ports, which pass through the chest wall and extend into the lS thoracic cavity, may be used for introducing and subsequent manipulating and fixing to tissue on or around the heart the patch electrode of this invention. The thoracoscopic ports 42 and 44, which typically have an internal diameter of 10 to 15 millimeters, may be placed in any of several intercostal locations, including those shown in FIG. 14. By way of introduction through the thoracoscopic ports, multiply electrically common electrodes 46 and 48 constructed in accordance with this invention are positioned on the left heart. The electrodes 46 and 48 are connected through an adaptor S0 to the negative terminal of an implantable pulse generator unit ~not shown). A single electrode 52 is shown positioned on the heart and connected to the positive terminal of 21072~
'a~ implantable pulse generator unit (not shown).
Larger patch electrodes, having a surface area in the range of 20 to 40 sq. cm. may have more than one mesh-free region so that the electrode may be folded in a "pleated" fashion to decrease the profile of the electrode for introduction.
Referring to FIGS. 6 and 7, an electrode in accordance with this invention with three substantially, parallel mesh conductors 54, 56, and 58 is shown. An electrode constructed in this manner has two parallel "conductor-free" zones. Referring to ~IG. 7, the electrode of FIG. 6 is shown in its folded or pleaded state for deployment using minimally invasive techniques. The dashed lines in FIG. 7 show the unstressed, planar shape of the electrode as it appears in use. As shown in FIG. 6, tabs 60 which extend beyond the border of the electrode portion 12 provide a convenient means of fixation to tissues for electrode immobiliza-tion. The tabs are typically formed of Dacron~ reinforced silicone rubber sheeting 0.25 to 1 millimeter thick, or a suitable porous, tissue-in-growth-promoting fabric such as Dacron~. The tabs are ~o fixed to the tissue by using staples or sutures, either solely or in combination.
While mesh type conductive elements have been illustrated and described with respect to the embodiments of the invention shown in FIGS. 1 through ~, the use of other types of conductive elements is encompassed within the invention. Conductive elements other than mesh which could be used are foils, wires or preferably 21 072~
~~ulti-filar coils (0.5 to 2.5 millimeters major diameter) which are embedded in the insulative backing.
FIG. 8 shows a electrode assembly in accordance with this invention wherein two loops 62 and 64 of multi-filar coils are located on either side of a centerline 32 of the back-ing element 20, along which the electrode assembly may be folded for implanta-tion.
As shown in FIGS. 9 and 10, the electrode assembly shown in FIG. 8 may be provided with ribs to augment the spring force of the conductor-free zone. The ribs 66 have a height of 1 to 5 times the thickness of the backing element 20 and are placed generally perpendicular to the centerline 32 of the backing element. The ribs 66 are preferably formed of silicone rubber of the same or higher durometer compared to the material of which the backing element 20 is formed and should nominally be two to ten times the backing element 20 thickness in width. The effect of the ribs 66 is to increase the spring-like return force generated by the conductor-free zone. With the use of the ribs, the electrode portion is more forcefully returned to a planar state when the deformation forces of implantation are removed.
FIG. 11 shows still another embodiment of this invention wherein three strands of multi-filar coils are located on the backing element parallel to each other. The patch electrode of FIG. 11 is shown in its relaxed or implanted orientation in FIG.
12, and in the folded or spring loaded orientation in which it is placed during an intrathoracic introduction procedure in FIG. 13.
~~ The above description is2 ~e7n~ed by way of example only and is not intended to limit the present invention in any way except as set forth in the accompanying claims.
, - . . .
Claims (13)
1. A cardioversion/defibrillation patch electrode for insertion through a thoracoscopic port comprising:
an insulative element having first and second opposing surfaces, and at least two electrically conductive elements disposed on said first surface of said insulative element and separated from each other by a conductor-free region of said first surface of said insulative element, said conductor-free region defining a hinge about which the electrode is caused to bend by deformation forces encountered during implantation from a substantially planar orientation in a relaxed state to folded, springy orientation, said springy orientation causing said electrode to return to said substantially planar configuration when said deformation forces are removed.
an insulative element having first and second opposing surfaces, and at least two electrically conductive elements disposed on said first surface of said insulative element and separated from each other by a conductor-free region of said first surface of said insulative element, said conductor-free region defining a hinge about which the electrode is caused to bend by deformation forces encountered during implantation from a substantially planar orientation in a relaxed state to folded, springy orientation, said springy orientation causing said electrode to return to said substantially planar configuration when said deformation forces are removed.
2. The electrode of claim 1, wherein said at least two conductive elements are substantially coplanar when the electrode is in the substantially planar orientation.
3. The electrode of claim 2, wherein the electrode may bend through approximately 180 degrees such that said at least two electrically conductive elements are substantially parallel to one another in the folded orientation.
4. The electrode of claim 1, having more than two conductor-free regions separating more than two electrically conductive elements disposed on said first surface.
5. The electrode of claim 1, wherein the electrically conductive elements are formed of a conductive mesh.
6. The electrode of claim 1, wherein the electrically conductive elements are formed of foils.
7. The electrode of claim 1, wherein the electrically conductive elements are formed of multi-filar coils.
8. The electrode of claim 1, wherein at least one rib is provided on said second surface perpendicular to said hinge, to augment the spring force of said conductor-free regions.
9. A cardioversion/defibrillation electrode device for insertion through a thoracoscopic port comprising:
a lead comprising an elongated insulative member and a plurality of insulated conductors extending through said insulative member;
an electrode portion connected to said lead comprising:
an insulative element having first and second opposing surfaces; and at least two electrically conductive elements disposed on said first surface of said insulative element and separated from each other by a conductor-free region on said first surface of said insulative element, each of said electrically conductive elements being connected to a respective one of said insulative conductors, the conductor-free region defining a hinge about which the electrode portion is caused to bend by deformation forces encountered during implantation from a substantially planar orientation in a relaxed state to a folded, springy orientation, said springy orientation causing said electrode to return to said substantially planar configuration when said deformation forces are removed.
a lead comprising an elongated insulative member and a plurality of insulated conductors extending through said insulative member;
an electrode portion connected to said lead comprising:
an insulative element having first and second opposing surfaces; and at least two electrically conductive elements disposed on said first surface of said insulative element and separated from each other by a conductor-free region on said first surface of said insulative element, each of said electrically conductive elements being connected to a respective one of said insulative conductors, the conductor-free region defining a hinge about which the electrode portion is caused to bend by deformation forces encountered during implantation from a substantially planar orientation in a relaxed state to a folded, springy orientation, said springy orientation causing said electrode to return to said substantially planar configuration when said deformation forces are removed.
10. The electrode device of claim 9, further comprising a terminal pin at a proximal end of said lead, each of said insulated conductors electrically connected to said terminal pin.
11. The electrode device of claim 9, wherein said at least two conductive elements are substantially coplanar when said electrode portion is in the substantially planar orientation.
12. The electrode device of claim 11, wherein said electrode portion may bend through approximately 180 degrees such that said at least two electrically conductive elements are substantially parallel to one another in the folded orientation.
13. A cardioversion/defibrillation path electrode assembly comprising:
an insertable thoracoscopic tube; and an electrode folded within said insertable thoracoscopic tube, the electrode further comprising:
an insulative element having first and second opposing surfaces; and at least two electrically conductive elements disposed on said first surface of said insulative element and separated from each other by a conductor-free region of said first surface of said insulative element, said conductor-free region defining a hinge about which the electrode is caused to bend from a folded, springy orientation within the insertable thoracoscopic tube to a substantially planar orientation in a relaxed state outside said insertable thoracoscopic tube.
an insertable thoracoscopic tube; and an electrode folded within said insertable thoracoscopic tube, the electrode further comprising:
an insulative element having first and second opposing surfaces; and at least two electrically conductive elements disposed on said first surface of said insulative element and separated from each other by a conductor-free region of said first surface of said insulative element, said conductor-free region defining a hinge about which the electrode is caused to bend from a folded, springy orientation within the insertable thoracoscopic tube to a substantially planar orientation in a relaxed state outside said insertable thoracoscopic tube.
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US95461692A | 1992-09-30 | 1992-09-30 | |
US07/954,616 | 1992-09-30 |
Publications (2)
Publication Number | Publication Date |
---|---|
CA2107246A1 CA2107246A1 (en) | 1994-03-31 |
CA2107246C true CA2107246C (en) | 1998-08-25 |
Family
ID=25495690
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
CA002107246A Expired - Fee Related CA2107246C (en) | 1992-09-30 | 1993-09-29 | Defibrillation patch electrode having conductor-free resilient zone for minimally invasive deployment |
Country Status (7)
Country | Link |
---|---|
US (1) | US5391200A (en) |
EP (1) | EP0590431B1 (en) |
JP (1) | JP2744879B2 (en) |
AT (1) | ATE176404T1 (en) |
AU (1) | AU653107B2 (en) |
CA (1) | CA2107246C (en) |
DE (1) | DE69323374T2 (en) |
Families Citing this family (259)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5496362A (en) * | 1992-11-24 | 1996-03-05 | Cardiac Pacemakers, Inc. | Implantable conformal coil patch electrode with multiple conductive elements for cardioversion and defibrillation |
US5840076A (en) * | 1996-04-12 | 1998-11-24 | Ep Technologies, Inc. | Tissue heating and ablation systems and methods using electrode structures with distally oriented porous regions |
US5797903A (en) * | 1996-04-12 | 1998-08-25 | Ep Technologies, Inc. | Tissue heating and ablation systems and methods using porous electrode structures with electrically conductive surfaces |
US5509924A (en) * | 1994-04-12 | 1996-04-23 | Ventritex, Inc. | Epicardial stimulation electrode with energy directing capability |
NL1001890C2 (en) * | 1995-12-13 | 1997-06-17 | Cordis Europ | Catheter with plate-shaped electrode array. |
US5776072A (en) * | 1995-12-28 | 1998-07-07 | Cardiac Pacemakers, Inc. | Discrimination of atrial and ventricular signals from a single cardiac lead |
US5836874A (en) * | 1996-04-08 | 1998-11-17 | Ep Technologies, Inc. | Multi-function electrode structures for electrically analyzing and heating body tissue |
US5846238A (en) * | 1996-01-19 | 1998-12-08 | Ep Technologies, Inc. | Expandable-collapsible electrode structures with distal end steering or manipulation |
US5830213A (en) * | 1996-04-12 | 1998-11-03 | Ep Technologies, Inc. | Systems for heating and ablating tissue using multifunctional electrode structures |
US5961513A (en) * | 1996-01-19 | 1999-10-05 | Ep Technologies, Inc. | Tissue heating and ablation systems and methods using porous electrode structures |
US5871483A (en) * | 1996-01-19 | 1999-02-16 | Ep Technologies, Inc. | Folding electrode structures |
US5868736A (en) * | 1996-04-12 | 1999-02-09 | Ep Technologies, Inc. | Systems and methods to control tissue heating or ablation with porous electrode structures |
US5891136A (en) * | 1996-01-19 | 1999-04-06 | Ep Technologies, Inc. | Expandable-collapsible mesh electrode structures |
US6475213B1 (en) | 1996-01-19 | 2002-11-05 | Ep Technologies, Inc. | Method of ablating body tissue |
US5853411A (en) * | 1996-01-19 | 1998-12-29 | Ep Technologies, Inc. | Enhanced electrical connections for electrode structures |
US5925038A (en) * | 1996-01-19 | 1999-07-20 | Ep Technologies, Inc. | Expandable-collapsible electrode structures for capacitive coupling to tissue |
US6071278A (en) * | 1996-02-28 | 2000-06-06 | Ep Technologies, Inc. | Tissue heating and ablation systems and methods using porous electrode structures with specified electrical resistivities |
WO1997025918A1 (en) * | 1996-01-19 | 1997-07-24 | Ep Technologies, Inc. | Electrode structures formed from flexible, porous, or woven materials |
US5846239A (en) * | 1996-04-12 | 1998-12-08 | Ep Technologies, Inc. | Tissue heating and ablation systems and methods using segmented porous electrode structures |
US5879348A (en) * | 1996-04-12 | 1999-03-09 | Ep Technologies, Inc. | Electrode structures formed from flexible, porous, or woven materials |
US5891135A (en) * | 1996-01-19 | 1999-04-06 | Ep Technologies, Inc. | Stem elements for securing tubing and electrical wires to expandable-collapsible electrode structures |
US5904711A (en) * | 1996-02-08 | 1999-05-18 | Heartport, Inc. | Expandable thoracoscopic defibrillation catheter system and method |
US6152954A (en) | 1998-07-22 | 2000-11-28 | Cardiac Pacemakers, Inc. | Single pass lead having retractable, actively attached electrode for pacing and sensing |
US6501994B1 (en) * | 1997-12-24 | 2002-12-31 | Cardiac Pacemakers, Inc. | High impedance electrode tip |
US6522932B1 (en) | 1998-02-10 | 2003-02-18 | Advanced Bionics Corporation | Implantable, expandable, multicontact electrodes and tools for use therewith |
US6205361B1 (en) * | 1998-02-10 | 2001-03-20 | Advanced Bionics Corporation | Implantable expandable multicontact electrodes |
US6415187B1 (en) * | 1998-02-10 | 2002-07-02 | Advanced Bionics Corporation | Implantable, expandable, multicontact electrodes and insertion needle for use therewith |
US6432104B1 (en) * | 1998-04-15 | 2002-08-13 | Scimed Life Systems, Inc. | Electro-cautery catherer |
US6325800B1 (en) | 1998-04-15 | 2001-12-04 | Boston Scientific Corporation | Electro-cautery catheter |
US6319241B1 (en) | 1998-04-30 | 2001-11-20 | Medtronic, Inc. | Techniques for positioning therapy delivery elements within a spinal cord or a brain |
US6161047A (en) | 1998-04-30 | 2000-12-12 | Medtronic Inc. | Apparatus and method for expanding a stimulation lead body in situ |
US6110196A (en) * | 1998-06-17 | 2000-08-29 | Edwards; Stuart D. | Apparatus and method for tympanic membrane tightening |
US6501990B1 (en) * | 1999-12-23 | 2002-12-31 | Cardiac Pacemakers, Inc. | Extendable and retractable lead having a snap-fit terminal connector |
US6463334B1 (en) * | 1998-11-02 | 2002-10-08 | Cardiac Pacemakers, Inc. | Extendable and retractable lead |
US6606523B1 (en) * | 1999-04-14 | 2003-08-12 | Transneuronix Inc. | Gastric stimulator apparatus and method for installing |
DE19930268A1 (en) * | 1999-06-25 | 2001-01-04 | Biotronik Mess & Therapieg | Flexible, rollable flat electrode for defibrillator, used with implantation catheter for introduction and release in pericardial cavity, has elasticity such that it is self-unrolling by elastic resilience |
EP1218056A1 (en) * | 1999-09-27 | 2002-07-03 | Theracardia, Inc. | Methods and apparatus for deploying cardiac electrodes and for electrical treatment |
US7065407B2 (en) | 2000-09-18 | 2006-06-20 | Cameron Health, Inc. | Duckbill-shaped implantable cardioverter-defibrillator canister and method of use |
US7090682B2 (en) | 2000-09-18 | 2006-08-15 | Cameron Health, Inc. | Method and apparatus for extraction of a subcutaneous electrode |
US6937907B2 (en) * | 2000-09-18 | 2005-08-30 | Cameron Health, Inc. | Subcutaneous electrode for transthoracic conduction with low-profile installation appendage and method of doing same |
US7146212B2 (en) * | 2000-09-18 | 2006-12-05 | Cameron Health, Inc. | Anti-bradycardia pacing for a subcutaneous implantable cardioverter-defibrillator |
US6988003B2 (en) * | 2000-09-18 | 2006-01-17 | Cameron Health, Inc. | Implantable cardioverter-defibrillator having two spaced apart shocking electrodes on housing |
US7194302B2 (en) * | 2000-09-18 | 2007-03-20 | Cameron Health, Inc. | Subcutaneous cardiac stimulator with small contact surface electrodes |
US7076296B2 (en) * | 2000-09-18 | 2006-07-11 | Cameron Health, Inc. | Method of supplying energy to subcutaneous cardioverter-defibrillator and pacer |
US6721597B1 (en) * | 2000-09-18 | 2004-04-13 | Cameron Health, Inc. | Subcutaneous only implantable cardioverter defibrillator and optional pacer |
US7069080B2 (en) * | 2000-09-18 | 2006-06-27 | Cameron Health, Inc. | Active housing and subcutaneous electrode cardioversion/defibrillating system |
US20020035379A1 (en) | 2000-09-18 | 2002-03-21 | Bardy Gust H. | Subcutaneous electrode for transthoracic conduction with improved installation characteristics |
US7039465B2 (en) | 2000-09-18 | 2006-05-02 | Cameron Health, Inc. | Ceramics and/or other material insulated shell for active and non-active S-ICD can |
US6856835B2 (en) * | 2000-09-18 | 2005-02-15 | Cameron Health, Inc. | Biphasic waveform for anti-tachycardia pacing for a subcutaneous implantable cardioverter-defibrillator |
US6952610B2 (en) * | 2000-09-18 | 2005-10-04 | Cameron Health, Inc. | Current waveforms for anti-tachycardia pacing for a subcutaneous implantable cardioverter- defibrillator |
US20020035381A1 (en) | 2000-09-18 | 2002-03-21 | Cameron Health, Inc. | Subcutaneous electrode with improved contact shape for transthoracic conduction |
US6950705B2 (en) | 2000-09-18 | 2005-09-27 | Cameron Health, Inc. | Canister designs for implantable cardioverter-defibrillators |
US6866044B2 (en) | 2000-09-18 | 2005-03-15 | Cameron Health, Inc. | Method of insertion and implantation of implantable cardioverter-defibrillator canisters |
US7194309B2 (en) * | 2000-09-18 | 2007-03-20 | Cameron Health, Inc. | Packaging technology for non-transvenous cardioverter/defibrillator devices |
US20020095184A1 (en) * | 2000-09-18 | 2002-07-18 | Bardy Gust H. | Monophasic waveform for anti-tachycardia pacing for a subcutaneous implantable cardioverter-defibrillator |
US6778860B2 (en) | 2001-11-05 | 2004-08-17 | Cameron Health, Inc. | Switched capacitor defibrillation circuit |
US7751885B2 (en) * | 2000-09-18 | 2010-07-06 | Cameron Health, Inc. | Bradycardia pacing in a subcutaneous device |
US6927721B2 (en) * | 2001-11-05 | 2005-08-09 | Cameron Health, Inc. | Low power A/D converter |
US20020035378A1 (en) * | 2000-09-18 | 2002-03-21 | Cameron Health, Inc. | Subcutaneous electrode for transthoracic conduction with highly maneuverable insertion tool |
US7043299B2 (en) * | 2000-09-18 | 2006-05-09 | Cameron Health, Inc. | Subcutaneous implantable cardioverter-defibrillator employing a telescoping lead |
US7149575B2 (en) * | 2000-09-18 | 2006-12-12 | Cameron Health, Inc. | Subcutaneous cardiac stimulator device having an anteriorly positioned electrode |
US20020107544A1 (en) * | 2000-09-18 | 2002-08-08 | Cameron Health, Inc. | Current waveform for anti-bradycardia pacing for a subcutaneous implantable cardioverter-defibrillator |
US6788974B2 (en) * | 2000-09-18 | 2004-09-07 | Cameron Health, Inc. | Radian curve shaped implantable cardioverter-defibrillator canister |
US6834204B2 (en) | 2001-11-05 | 2004-12-21 | Cameron Health, Inc. | Method and apparatus for inducing defibrillation in a patient using a T-shock waveform |
US20020035377A1 (en) * | 2000-09-18 | 2002-03-21 | Cameron Health, Inc. | Subcutaneous electrode for transthoracic conduction with insertion tool |
US6754528B2 (en) | 2001-11-21 | 2004-06-22 | Cameraon Health, Inc. | Apparatus and method of arrhythmia detection in a subcutaneous implantable cardioverter/defibrillator |
US7120495B2 (en) | 2000-09-18 | 2006-10-10 | Cameron Health, Inc. | Flexible subcutaneous implantable cardioverter-defibrillator |
US7130682B2 (en) | 2000-12-26 | 2006-10-31 | Cardiac Pacemakers, Inc. | Pacing and sensing vectors |
US7330757B2 (en) * | 2001-11-21 | 2008-02-12 | Cameron Health, Inc. | Method for discriminating between ventricular and supraventricular arrhythmias |
US7392085B2 (en) * | 2001-11-21 | 2008-06-24 | Cameron Health, Inc. | Multiple electrode vectors for implantable cardiac treatment devices |
US7248921B2 (en) | 2003-06-02 | 2007-07-24 | Cameron Health, Inc. | Method and devices for performing cardiac waveform appraisal |
US6829510B2 (en) * | 2001-12-18 | 2004-12-07 | Ness Neuromuscular Electrical Stimulation Systems Ltd. | Surface neuroprosthetic device having an internal cushion interface system |
US6980858B2 (en) * | 2001-12-31 | 2005-12-27 | Biosense Webster, Inc. | Method and system for atrial defibrillation |
US7270669B1 (en) * | 2002-03-14 | 2007-09-18 | Medtronic, Inc. | Epicardial lead placement for bi-ventricular pacing using thoracoscopic approach |
US7697995B2 (en) * | 2002-04-25 | 2010-04-13 | Medtronic, Inc. | Surgical lead paddle |
US7110815B2 (en) * | 2002-05-06 | 2006-09-19 | Cardiac Pacemakers, Inc. | System and method for providing temporary stimulation therapy to optimize chronic electrical performance for electrodes used in conjunction with a cardiac rhythm management system |
US20050080348A1 (en) * | 2003-09-18 | 2005-04-14 | Stahmann Jeffrey E. | Medical event logbook system and method |
US7392081B2 (en) * | 2003-02-28 | 2008-06-24 | Cardiac Pacemakers, Inc. | Subcutaneous cardiac stimulator employing post-shock transthoracic asystole prevention pacing |
US20040199082A1 (en) * | 2003-04-03 | 2004-10-07 | Ostroff Alan H. | Selctable notch filter circuits |
US7566318B2 (en) * | 2003-04-11 | 2009-07-28 | Cardiac Pacemakers, Inc. | Ultrasonic subcutaneous dissection tool incorporating fluid delivery |
US8116868B2 (en) | 2003-04-11 | 2012-02-14 | Cardiac Pacemakers, Inc. | Implantable device with cardiac event audio playback |
US7865233B2 (en) | 2003-04-11 | 2011-01-04 | Cardiac Pacemakers, Inc. | Subcutaneous cardiac signal discrimination employing non-electrophysiologic signal |
US7389138B2 (en) * | 2003-04-11 | 2008-06-17 | Cardiac Pacemakers, Inc. | Electrode placement determination for subcutaneous cardiac monitoring and therapy |
US20040215240A1 (en) * | 2003-04-11 | 2004-10-28 | Lovett Eric G. | Reconfigurable subcutaneous cardiac device |
US7236819B2 (en) | 2003-04-11 | 2007-06-26 | Cardiac Pacemakers, Inc. | Separation of a subcutaneous cardiac signal from a plurality of composite signals |
US20040220628A1 (en) * | 2003-04-11 | 2004-11-04 | Wagner Darrell Orvin | Subcutaneous defibrillation timing correlated with induced skeletal muscle contraction |
US20040230230A1 (en) * | 2003-04-11 | 2004-11-18 | Lindstrom Curtis Charles | Methods and systems involving subcutaneous electrode positioning relative to a heart |
US7218966B2 (en) * | 2003-04-11 | 2007-05-15 | Cardiac Pacemakers, Inc. | Multi-parameter arrhythmia discrimination |
US7499758B2 (en) * | 2003-04-11 | 2009-03-03 | Cardiac Pacemakers, Inc. | Helical fixation elements for subcutaneous electrodes |
US7555335B2 (en) | 2003-04-11 | 2009-06-30 | Cardiac Pacemakers, Inc. | Biopotential signal source separation using source impedances |
US7117035B2 (en) | 2003-04-11 | 2006-10-03 | Cardiac Pacemakers, Inc. | Subcutaneous cardiac stimulation system with patient activity sensing |
US20040230272A1 (en) * | 2003-04-11 | 2004-11-18 | Cates Adam W. | Subcutaneous lead with temporary pharmacological agents |
US20040204735A1 (en) * | 2003-04-11 | 2004-10-14 | Shiroff Jason Alan | Subcutaneous dissection tool incorporating pharmacological agent delivery |
US7979122B2 (en) | 2003-04-11 | 2011-07-12 | Cardiac Pacemakers, Inc. | Implantable sudden cardiac death prevention device with reduced programmable feature set |
US20050004615A1 (en) * | 2003-04-11 | 2005-01-06 | Sanders Richard S. | Reconfigurable implantable cardiac monitoring and therapy delivery device |
US7302294B2 (en) | 2003-04-11 | 2007-11-27 | Cardiac Pacemakers, Inc. | Subcutaneous cardiac sensing and stimulation system employing blood sensor |
US7702399B2 (en) * | 2003-04-11 | 2010-04-20 | Cardiac Pacemakers, Inc. | Subcutaneous electrode and lead with phoresis based pharmacological agent delivery |
US7529592B2 (en) | 2003-04-11 | 2009-05-05 | Cardiac Pacemakers, Inc. | Subcutaneous electrode and lead with temporary pharmacological agents |
US7493175B2 (en) | 2003-04-11 | 2009-02-17 | Cardiac Pacemakers, Inc. | Subcutaneous lead with tined fixation |
US20040220626A1 (en) * | 2003-04-11 | 2004-11-04 | Wagner Darrell Orvin | Distributed subcutaneous defibrillation system |
US20040204734A1 (en) * | 2003-04-11 | 2004-10-14 | Wagner Darrell Orvin | Tunneling tool with subcutaneous transdermal illumination |
US7349742B2 (en) * | 2003-04-11 | 2008-03-25 | Cardiac Pacemakers, Inc. | Expandable fixation elements for subcutaneous electrodes |
US7047071B2 (en) | 2003-04-11 | 2006-05-16 | Cardiac Pacemakers, Inc. | Patient stratification for implantable subcutaneous cardiac monitoring and therapy |
US7499750B2 (en) * | 2003-04-11 | 2009-03-03 | Cardiac Pacemakers, Inc. | Noise canceling cardiac electrodes |
US7570997B2 (en) | 2003-04-11 | 2009-08-04 | Cardiac Pacemakers, Inc. | Subcutaneous cardiac rhythm management with asystole prevention therapy |
US7477932B2 (en) | 2003-05-28 | 2009-01-13 | Cardiac Pacemakers, Inc. | Cardiac waveform template creation, maintenance and use |
US8251061B2 (en) * | 2003-09-18 | 2012-08-28 | Cardiac Pacemakers, Inc. | Methods and systems for control of gas therapy |
US20050142070A1 (en) * | 2003-09-18 | 2005-06-30 | Hartley Jesse W. | Methods and systems for assessing pulmonary disease with drug therapy control |
US7668591B2 (en) * | 2003-09-18 | 2010-02-23 | Cardiac Pacemakers, Inc. | Automatic activation of medical processes |
US7591265B2 (en) | 2003-09-18 | 2009-09-22 | Cardiac Pacemakers, Inc. | Coordinated use of respiratory and cardiac therapies for sleep disordered breathing |
US7787946B2 (en) * | 2003-08-18 | 2010-08-31 | Cardiac Pacemakers, Inc. | Patient monitoring, diagnosis, and/or therapy systems and methods |
US7967756B2 (en) * | 2003-09-18 | 2011-06-28 | Cardiac Pacemakers, Inc. | Respiratory therapy control based on cardiac cycle |
US8606356B2 (en) * | 2003-09-18 | 2013-12-10 | Cardiac Pacemakers, Inc. | Autonomic arousal detection system and method |
US7757690B2 (en) * | 2003-09-18 | 2010-07-20 | Cardiac Pacemakers, Inc. | System and method for moderating a therapy delivered during sleep using physiologic data acquired during non-sleep |
US7396333B2 (en) * | 2003-08-18 | 2008-07-08 | Cardiac Pacemakers, Inc. | Prediction of disordered breathing |
US7616988B2 (en) * | 2003-09-18 | 2009-11-10 | Cardiac Pacemakers, Inc. | System and method for detecting an involuntary muscle movement disorder |
US7720541B2 (en) * | 2003-08-18 | 2010-05-18 | Cardiac Pacemakers, Inc. | Adaptive therapy for disordered breathing |
US20050107838A1 (en) * | 2003-09-18 | 2005-05-19 | Lovett Eric G. | Subcutaneous cardiac rhythm management with disordered breathing detection and treatment |
US7510531B2 (en) | 2003-09-18 | 2009-03-31 | Cardiac Pacemakers, Inc. | System and method for discrimination of central and obstructive disordered breathing events |
US7532934B2 (en) * | 2003-09-18 | 2009-05-12 | Cardiac Pacemakers, Inc. | Snoring detection system and method |
US7678061B2 (en) | 2003-09-18 | 2010-03-16 | Cardiac Pacemakers, Inc. | System and method for characterizing patient respiration |
US7664546B2 (en) * | 2003-09-18 | 2010-02-16 | Cardiac Pacemakers, Inc. | Posture detection system and method |
US7662101B2 (en) * | 2003-09-18 | 2010-02-16 | Cardiac Pacemakers, Inc. | Therapy control based on cardiopulmonary status |
US7887493B2 (en) | 2003-09-18 | 2011-02-15 | Cardiac Pacemakers, Inc. | Implantable device employing movement sensing for detecting sleep-related disorders |
US7468040B2 (en) * | 2003-09-18 | 2008-12-23 | Cardiac Pacemakers, Inc. | Methods and systems for implantably monitoring external breathing therapy |
US7575553B2 (en) * | 2003-09-18 | 2009-08-18 | Cardiac Pacemakers, Inc. | Methods and systems for assessing pulmonary disease |
US7680537B2 (en) * | 2003-08-18 | 2010-03-16 | Cardiac Pacemakers, Inc. | Therapy triggered by prediction of disordered breathing |
US7970470B2 (en) * | 2003-09-18 | 2011-06-28 | Cardiac Pacemakers, Inc. | Diagnosis and/or therapy using blood chemistry/expired gas parameter analysis |
US7610094B2 (en) * | 2003-09-18 | 2009-10-27 | Cardiac Pacemakers, Inc. | Synergistic use of medical devices for detecting medical disorders |
US7469697B2 (en) * | 2003-09-18 | 2008-12-30 | Cardiac Pacemakers, Inc. | Feedback system and method for sleep disordered breathing therapy |
US7572225B2 (en) * | 2003-09-18 | 2009-08-11 | Cardiac Pacemakers, Inc. | Sleep logbook |
EP1667586A1 (en) | 2003-09-15 | 2006-06-14 | Abbott Laboratories | Suture locking device and methods |
US20050075707A1 (en) * | 2003-09-16 | 2005-04-07 | Meadows Paul M. | Axial to planar lead conversion device and method |
US20050080470A1 (en) * | 2003-10-09 | 2005-04-14 | Randy Westlund | Intramyocardial lead implantation system and method |
US7437197B2 (en) * | 2003-10-23 | 2008-10-14 | Medtronic, Inc. | Medical lead and manufacturing method therefor |
US20050288715A1 (en) * | 2003-11-07 | 2005-12-29 | Lilip Lau | Cardiac harness for treating congestive heart failure and for defibrillating and/or pacing/sensing |
US20070106359A1 (en) * | 2003-11-07 | 2007-05-10 | Alan Schaer | Cardiac harness assembly for treating congestive heart failure and for pacing/sensing |
US20060009831A1 (en) * | 2003-11-07 | 2006-01-12 | Lilip Lau | Cardiac harness having leadless electrodes for pacing and sensing therapy |
US7319900B2 (en) * | 2003-12-11 | 2008-01-15 | Cardiac Pacemakers, Inc. | Cardiac response classification using multiple classification windows |
US7197362B2 (en) * | 2003-12-11 | 2007-03-27 | Cardiac Pacemakers, Inc. | Cardiac lead having coated fixation arrangement |
US20060247693A1 (en) | 2005-04-28 | 2006-11-02 | Yanting Dong | Non-captured intrinsic discrimination in cardiac pacing response classification |
US7774064B2 (en) * | 2003-12-12 | 2010-08-10 | Cardiac Pacemakers, Inc. | Cardiac response classification using retriggerable classification windows |
US8521284B2 (en) | 2003-12-12 | 2013-08-27 | Cardiac Pacemakers, Inc. | Cardiac response classification using multisite sensing and pacing |
US20050137646A1 (en) * | 2003-12-22 | 2005-06-23 | Scimed Life Systems, Inc. | Method of intravascularly delivering stimulation leads into brain |
US8060207B2 (en) | 2003-12-22 | 2011-11-15 | Boston Scientific Scimed, Inc. | Method of intravascularly delivering stimulation leads into direct contact with tissue |
US7295875B2 (en) * | 2004-02-20 | 2007-11-13 | Boston Scientific Scimed, Inc. | Method of stimulating/sensing brain with combination of intravascularly and non-vascularly delivered leads |
US20050215884A1 (en) * | 2004-02-27 | 2005-09-29 | Greicius Michael D | Evaluation of Alzheimer's disease using an independent component analysis of an individual's resting-state functional MRI |
US20050203600A1 (en) | 2004-03-12 | 2005-09-15 | Scimed Life Systems, Inc. | Collapsible/expandable tubular electrode leads |
US7590454B2 (en) * | 2004-03-12 | 2009-09-15 | Boston Scientific Neuromodulation Corporation | Modular stimulation lead network |
US7177702B2 (en) | 2004-03-12 | 2007-02-13 | Scimed Life Systems, Inc. | Collapsible/expandable electrode leads |
US7255675B2 (en) * | 2004-03-23 | 2007-08-14 | Michael Gertner | Devices and methods to treat a patient |
US8224459B1 (en) | 2004-04-30 | 2012-07-17 | Boston Scientific Neuromodulation Corporation | Insertion tool for paddle-style electrode |
US8706259B2 (en) | 2004-04-30 | 2014-04-22 | Boston Scientific Neuromodulation Corporation | Insertion tool for paddle-style electrode |
KR100601953B1 (en) * | 2004-05-03 | 2006-07-14 | 삼성전자주식회사 | Capacitor of memory device and fabrication method thereof |
US8412348B2 (en) * | 2004-05-06 | 2013-04-02 | Boston Scientific Neuromodulation Corporation | Intravascular self-anchoring integrated tubular electrode body |
US7747323B2 (en) | 2004-06-08 | 2010-06-29 | Cardiac Pacemakers, Inc. | Adaptive baroreflex stimulation therapy for disordered breathing |
US7596413B2 (en) * | 2004-06-08 | 2009-09-29 | Cardiac Pacemakers, Inc. | Coordinated therapy for disordered breathing including baroreflex modulation |
US7706866B2 (en) * | 2004-06-24 | 2010-04-27 | Cardiac Pacemakers, Inc. | Automatic orientation determination for ECG measurements using multiple electrodes |
US7286879B2 (en) | 2004-07-16 | 2007-10-23 | Boston Scientific Scimed, Inc. | Method of stimulating fastigium nucleus to treat neurological disorders |
US7823219B2 (en) * | 2004-09-27 | 2010-11-02 | Angiosome, Inc. | Decubitus ulcer prevention and treatment |
US7890159B2 (en) * | 2004-09-30 | 2011-02-15 | Cardiac Pacemakers, Inc. | Cardiac activation sequence monitoring and tracking |
US7917196B2 (en) * | 2005-05-09 | 2011-03-29 | Cardiac Pacemakers, Inc. | Arrhythmia discrimination using electrocardiograms sensed from multiple implanted electrodes |
US7805185B2 (en) * | 2005-05-09 | 2010-09-28 | Cardiac Pacemakers, In. | Posture monitoring using cardiac activation sequences |
US7509170B2 (en) * | 2005-05-09 | 2009-03-24 | Cardiac Pacemakers, Inc. | Automatic capture verification using electrocardiograms sensed from multiple implanted electrodes |
US7647108B2 (en) * | 2004-09-30 | 2010-01-12 | Cardiac Pacemakers, Inc. | Methods and systems for selection of cardiac pacing electrode configurations |
US7797036B2 (en) * | 2004-11-30 | 2010-09-14 | Cardiac Pacemakers, Inc. | Cardiac activation sequence monitoring for ischemia detection |
US7457664B2 (en) * | 2005-05-09 | 2008-11-25 | Cardiac Pacemakers, Inc. | Closed loop cardiac resynchronization therapy using cardiac activation sequence information |
US20060089681A1 (en) * | 2004-10-21 | 2006-04-27 | Cameron Health, Inc. | Implantable medical device |
US7477935B2 (en) * | 2004-11-29 | 2009-01-13 | Cameron Health, Inc. | Method and apparatus for beat alignment and comparison |
US7376458B2 (en) | 2004-11-29 | 2008-05-20 | Cameron Health, Inc. | Method for defining signal templates in implantable cardiac devices |
US7433739B1 (en) * | 2004-11-30 | 2008-10-07 | Pacesetter, Inc. | Passive fixation mechanism for epicardial sensing and stimulation lead placed through pericardial access |
US7655014B2 (en) * | 2004-12-06 | 2010-02-02 | Cameron Health, Inc. | Apparatus and method for subcutaneous electrode insertion |
US7937160B2 (en) * | 2004-12-10 | 2011-05-03 | Boston Scientific Neuromodulation Corporation | Methods for delivering cortical electrode leads into patient's head |
US7996072B2 (en) * | 2004-12-21 | 2011-08-09 | Cardiac Pacemakers, Inc. | Positionally adaptable implantable cardiac device |
JP2006185060A (en) * | 2004-12-27 | 2006-07-13 | Fujitsu Ltd | Method for inputting password |
US8160697B2 (en) * | 2005-01-25 | 2012-04-17 | Cameron Health, Inc. | Method for adapting charge initiation for an implantable cardioverter-defibrillator |
US8229563B2 (en) * | 2005-01-25 | 2012-07-24 | Cameron Health, Inc. | Devices for adapting charge initiation for an implantable cardioverter-defibrillator |
US7680534B2 (en) | 2005-02-28 | 2010-03-16 | Cardiac Pacemakers, Inc. | Implantable cardiac device with dyspnea measurement |
US7555338B2 (en) * | 2005-04-26 | 2009-06-30 | Cameron Health, Inc. | Methods and implantable devices for inducing fibrillation by alternating constant current |
US7392086B2 (en) * | 2005-04-26 | 2008-06-24 | Cardiac Pacemakers, Inc. | Implantable cardiac device and method for reduced phrenic nerve stimulation |
US7499751B2 (en) * | 2005-04-28 | 2009-03-03 | Cardiac Pacemakers, Inc. | Cardiac signal template generation using waveform clustering |
US7630755B2 (en) * | 2005-05-04 | 2009-12-08 | Cardiac Pacemakers Inc. | Syncope logbook and method of using same |
US8116867B2 (en) * | 2005-08-04 | 2012-02-14 | Cameron Health, Inc. | Methods and devices for tachyarrhythmia sensing and high-pass filter bypass |
US20070049975A1 (en) * | 2005-09-01 | 2007-03-01 | Cates Adam W | Active can with dedicated defibrillation and sensing electrodes |
US20070055115A1 (en) * | 2005-09-08 | 2007-03-08 | Jonathan Kwok | Characterization of sleep disorders using composite patient data |
US7731663B2 (en) * | 2005-09-16 | 2010-06-08 | Cardiac Pacemakers, Inc. | System and method for generating a trend parameter based on respiration rate distribution |
US8992436B2 (en) * | 2005-09-16 | 2015-03-31 | Cardiac Pacemakers, Inc. | Respiration monitoring using respiration rate variability |
US7775983B2 (en) * | 2005-09-16 | 2010-08-17 | Cardiac Pacemakers, Inc. | Rapid shallow breathing detection for use in congestive heart failure status determination |
US7927284B2 (en) * | 2005-09-16 | 2011-04-19 | Cardiac Pacemakers, Inc. | Quantifying hemodynamic response to drug therapy using implantable sensor |
US20070118180A1 (en) * | 2005-11-18 | 2007-05-24 | Quan Ni | Cardiac resynchronization therapy for improved hemodynamics based on disordered breathing detection |
US7479114B2 (en) | 2005-12-01 | 2009-01-20 | Cardiac Pacemakers, Inc. | Determining blood gas saturation based on measured parameter of respiration |
US7766840B2 (en) | 2005-12-01 | 2010-08-03 | Cardiac Pacemakers, Inc. | Method and system for heart failure status evaluation based on a disordered breathing index |
US20070135847A1 (en) * | 2005-12-12 | 2007-06-14 | Kenknight Bruce H | Subcutaneous defibrillation system and method using same |
US7662105B2 (en) | 2005-12-14 | 2010-02-16 | Cardiac Pacemakers, Inc. | Systems and methods for determining respiration metrics |
US7761158B2 (en) * | 2005-12-20 | 2010-07-20 | Cardiac Pacemakers, Inc. | Detection of heart failure decompensation based on cumulative changes in sensor signals |
US7922648B1 (en) * | 2006-02-14 | 2011-04-12 | Pacesetter, Inc. | Myocardial infarction patch for minimally invasive implant |
US7819816B2 (en) * | 2006-03-29 | 2010-10-26 | Cardiac Pacemakers, Inc. | Periodic disordered breathing detection |
US8200341B2 (en) | 2007-02-07 | 2012-06-12 | Cameron Health, Inc. | Sensing vector selection in a cardiac stimulus device with postural assessment |
US20070276452A1 (en) * | 2006-05-26 | 2007-11-29 | Cameron Health, Inc. | Implantable medical device systems having initialization functions and methods of operation |
US7783340B2 (en) | 2007-01-16 | 2010-08-24 | Cameron Health, Inc. | Systems and methods for sensing vector selection in an implantable medical device using a polynomial approach |
US7623909B2 (en) | 2006-05-26 | 2009-11-24 | Cameron Health, Inc. | Implantable medical devices and programmers adapted for sensing vector selection |
US8788023B2 (en) * | 2006-05-26 | 2014-07-22 | Cameron Health, Inc. | Systems and methods for sensing vector selection in an implantable medical device |
US8527048B2 (en) * | 2006-06-29 | 2013-09-03 | Cardiac Pacemakers, Inc. | Local and non-local sensing for cardiac pacing |
US20080004665A1 (en) * | 2006-06-29 | 2008-01-03 | Mccabe Aaron R | Determination of cardiac pacing parameters based on non-localized sensing |
US7599741B2 (en) * | 2006-06-29 | 2009-10-06 | Cardiac Pacemakers, Inc. | Systems and methods for improving heart rate kinetics in heart failure patients |
US20080015644A1 (en) * | 2006-07-14 | 2008-01-17 | Cameron Health, Inc. | End of life battery testing in an implantable medical device |
US7623913B2 (en) | 2006-08-01 | 2009-11-24 | Cameron Health, Inc. | Implantable medical devices using heuristic filtering in cardiac event detection |
US8718793B2 (en) | 2006-08-01 | 2014-05-06 | Cameron Health, Inc. | Electrode insertion tools, lead assemblies, kits and methods for placement of cardiac device electrodes |
US8209013B2 (en) * | 2006-09-14 | 2012-06-26 | Cardiac Pacemakers, Inc. | Therapeutic electrical stimulation that avoids undesirable activation |
US8948867B2 (en) | 2006-09-14 | 2015-02-03 | Cardiac Pacemakers, Inc. | Capture detection with cross chamber backup pacing |
US7877139B2 (en) | 2006-09-22 | 2011-01-25 | Cameron Health, Inc. | Method and device for implantable cardiac stimulus device lead impedance measurement |
US8014851B2 (en) * | 2006-09-26 | 2011-09-06 | Cameron Health, Inc. | Signal analysis in implantable cardiac treatment devices |
US7623916B2 (en) | 2006-12-20 | 2009-11-24 | Cameron Health, Inc. | Implantable cardiac stimulus devices and methods with input recharge circuitry |
US7797054B2 (en) | 2007-01-12 | 2010-09-14 | Medtronic, Inc. | Expandable systems for medical electrical stimulation |
DE102007009716B4 (en) * | 2007-02-28 | 2010-01-14 | Osypka, Peter, Dr. Ing. | Device for defibrillation of the heart |
US20080228093A1 (en) * | 2007-03-13 | 2008-09-18 | Yanting Dong | Systems and methods for enhancing cardiac signal features used in morphology discrimination |
US8052611B2 (en) | 2007-03-14 | 2011-11-08 | Cardiac Pacemakers, Inc. | Method and apparatus for management of heart failure hospitalization |
US8271080B2 (en) | 2007-05-23 | 2012-09-18 | Cardiac Pacemakers, Inc. | Decongestive therapy titration for heart failure patients using implantable sensor |
KR101513926B1 (en) * | 2007-07-06 | 2015-04-21 | 코비디엔 엘피 | Ablation in the gastrointestinal tract to achieve hemostasis and eradicate lesions with a propensity for bleeding |
KR100843249B1 (en) * | 2007-07-18 | 2008-07-02 | (주) 힐스코 | Stimulus apparatus using micro-current pulse |
US9037239B2 (en) | 2007-08-07 | 2015-05-19 | Cardiac Pacemakers, Inc. | Method and apparatus to perform electrode combination selection |
US8265736B2 (en) | 2007-08-07 | 2012-09-11 | Cardiac Pacemakers, Inc. | Method and apparatus to perform electrode combination selection |
US8192351B2 (en) | 2007-08-13 | 2012-06-05 | Paracor Medical, Inc. | Medical device delivery system having integrated introducer |
US9079033B2 (en) * | 2008-01-22 | 2015-07-14 | Cardiac Pacemakers, Inc. | Respiration as a trigger for therapy optimization |
EP2254661B1 (en) | 2008-02-14 | 2015-10-07 | Cardiac Pacemakers, Inc. | Apparatus for phrenic stimulation detection |
US20090281372A1 (en) * | 2008-05-06 | 2009-11-12 | Paracor Medical, Inc. | Cardiac harness assembly for treating congestive heart failure and for defibrillation and/or pacing/sensing |
US9795442B2 (en) | 2008-11-11 | 2017-10-24 | Shifamed Holdings, Llc | Ablation catheters |
WO2010056771A1 (en) * | 2008-11-11 | 2010-05-20 | Shifamed Llc | Low profile electrode assembly |
US8644927B2 (en) * | 2009-04-21 | 2014-02-04 | Incube Labs, Llc | Apparatus and method for the detection and treatment of atrial fibrillation |
EP2445568B1 (en) * | 2009-06-24 | 2020-09-23 | Kalila Medical, Inc. | Steerable medical delivery devices |
US20110009760A1 (en) * | 2009-07-10 | 2011-01-13 | Yi Zhang | Hospital Readmission Alert for Heart Failure Patients |
US9724126B2 (en) * | 2010-01-29 | 2017-08-08 | Medtronic, Inc. | Introduction of medical lead into patient |
US20110190858A1 (en) * | 2010-01-29 | 2011-08-04 | Medtronic, Inc. | Lead having expandable distal portion |
US8554339B2 (en) * | 2010-01-29 | 2013-10-08 | Medtronic, Inc. | Anchor assembly for use in occipital nerve stimulation |
US8801728B2 (en) | 2010-01-29 | 2014-08-12 | Medtronic, Inc. | Introduction of medical lead into patient |
AU2011232335A1 (en) | 2010-03-24 | 2012-10-11 | Shifamed Holdings, Llc | Intravascular tissue disruption |
US9655677B2 (en) | 2010-05-12 | 2017-05-23 | Shifamed Holdings, Llc | Ablation catheters including a balloon and electrodes |
CN105105844B (en) | 2010-05-12 | 2017-12-15 | 施菲姆德控股有限责任公司 | The electrode assemblie of little profile |
US9149265B2 (en) * | 2011-02-26 | 2015-10-06 | Abbott Cardiovascular Systems, Inc. | Hinged tissue support device |
WO2012151396A2 (en) | 2011-05-03 | 2012-11-08 | Shifamed Holdings, Llc | Steerable delivery sheaths |
KR101497458B1 (en) | 2011-08-25 | 2015-03-02 | 코비디엔 엘피 | Systems, devices, and methods for treatment of luminal tissue |
DE202011108639U1 (en) * | 2011-12-03 | 2012-01-16 | Peter Osypka | Implantable indifferent electrode |
US9138214B2 (en) | 2012-03-02 | 2015-09-22 | Abbott Cardiovascular Systems, Inc. | Suture securing systems, devices and methods |
US8961550B2 (en) | 2012-04-17 | 2015-02-24 | Indian Wells Medical, Inc. | Steerable endoluminal punch |
US9486132B2 (en) | 2013-01-17 | 2016-11-08 | Abbott Cardiovascular Systems, Inc. | Access device for accessing tissue |
EP2967404B1 (en) | 2013-03-11 | 2019-05-22 | Cameron Health, Inc. | Device implementing dual criteria for arrhythmia detection |
US9579065B2 (en) | 2013-03-12 | 2017-02-28 | Cameron Health Inc. | Cardiac signal vector selection with monophasic and biphasic shape consideration |
CA2908517A1 (en) | 2013-04-08 | 2014-10-16 | Apama Medical, Inc. | Cardiac ablation catheters and methods of use thereof |
US10349824B2 (en) | 2013-04-08 | 2019-07-16 | Apama Medical, Inc. | Tissue mapping and visualization systems |
US10098694B2 (en) | 2013-04-08 | 2018-10-16 | Apama Medical, Inc. | Tissue ablation and monitoring thereof |
EP3030143A1 (en) | 2013-08-05 | 2016-06-15 | Cardiac Pacemakers, Inc. | System and method for detecting worsening of heart failure based on rapid shallow breathing index |
US9867981B2 (en) | 2013-12-04 | 2018-01-16 | Boston Scientific Neuromodulation Corporation | Insertion tool for implanting a paddle lead and methods and systems utilizing the tool |
WO2016114923A1 (en) | 2015-01-13 | 2016-07-21 | Boston Scientific Neuromodulation Corporation | Insertion tool for implanting a paddle lead and methods and systems utilizing the tool |
WO2016160694A1 (en) | 2015-03-27 | 2016-10-06 | Shifamed Holdings, Llc | Steerable medical devices, systems, and methods of use |
CA2982823A1 (en) | 2015-04-24 | 2016-10-27 | Shifamed Holdings, Llc | Steerable medical devices, systems, and methods of use |
US10716500B2 (en) | 2015-06-29 | 2020-07-21 | Cardiac Pacemakers, Inc. | Systems and methods for normalization of chemical sensor data based on fluid state changes |
CN108366715A (en) | 2015-11-09 | 2018-08-03 | 施菲姆德控股有限责任公司 | Steering assembly and application method for medical treatment device |
EP3376936B1 (en) | 2015-11-16 | 2024-01-03 | Boston Scientific Scimed, Inc. | Energy delivery devices |
US11439383B2 (en) | 2019-08-20 | 2022-09-13 | Abbott Cardiovascular Systems, Inc. | Self locking suture and self locking suture mediated closure device |
Family Cites Families (14)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
GB617203A (en) * | 1945-07-11 | 1949-02-02 | Philips Nv | Improvements in or relating to high-frequency energy devices for medical purposes |
US3380445A (en) * | 1965-09-24 | 1968-04-30 | Int Rectifier Corp | Electrical pickup structure for electrocardiographs and the like |
US4144889A (en) * | 1977-05-31 | 1979-03-20 | Research Corporation | Cardiac electrodes for temporary pacing |
US4233987A (en) * | 1978-08-18 | 1980-11-18 | Alfred Feingold | Curvilinear electrocardiograph electrode strip |
DE3523226A1 (en) * | 1985-06-28 | 1987-01-08 | Osypka Peter | DEFIBRILLATION ELECTRODE |
DE3633803C2 (en) * | 1985-10-22 | 1995-10-19 | Telectronics Nv | Defibrillator electrode |
US4938231A (en) * | 1985-10-22 | 1990-07-03 | Telectronics N.V. | Defibrillator electrode |
US4827932A (en) * | 1987-02-27 | 1989-05-09 | Intermedics Inc. | Implantable defibrillation electrodes |
US4946457A (en) * | 1987-12-03 | 1990-08-07 | Dimed, Incorporated | Defibrillator system with cardiac leads and method for transvenous implantation |
US5042463A (en) * | 1990-05-23 | 1991-08-27 | Siemens-Pacesetter, Inc. | Patch electrode for heart defibrillator |
US5203348A (en) * | 1990-06-06 | 1993-04-20 | Cardiac Pacemakers, Inc. | Subcutaneous defibrillation electrodes |
DE4019002A1 (en) * | 1990-06-13 | 1992-01-02 | Siemens Ag | ELECTRODE ARRANGEMENT FOR A DEFIBRILLATOR |
US5190052A (en) * | 1990-11-21 | 1993-03-02 | Intermedics, Inc. | Pacer lead with bipolar electrode |
US5154182A (en) * | 1991-02-15 | 1992-10-13 | Siemens Pacesetter, Inc. | Drug or steroid releasing patch electrode for an implantable arrhythmia treatment system |
-
1993
- 1993-09-16 EP EP93114950A patent/EP0590431B1/en not_active Expired - Lifetime
- 1993-09-16 DE DE69323374T patent/DE69323374T2/en not_active Expired - Fee Related
- 1993-09-16 AT AT93114950T patent/ATE176404T1/en not_active IP Right Cessation
- 1993-09-20 AU AU47494/93A patent/AU653107B2/en not_active Ceased
- 1993-09-29 CA CA002107246A patent/CA2107246C/en not_active Expired - Fee Related
- 1993-09-30 JP JP5245085A patent/JP2744879B2/en not_active Expired - Fee Related
-
1994
- 1994-03-10 US US08/209,356 patent/US5391200A/en not_active Expired - Lifetime
Also Published As
Publication number | Publication date |
---|---|
AU4749493A (en) | 1994-04-28 |
EP0590431B1 (en) | 1999-02-03 |
AU653107B2 (en) | 1994-09-15 |
DE69323374T2 (en) | 1999-06-10 |
US5391200A (en) | 1995-02-21 |
JPH06277299A (en) | 1994-10-04 |
ATE176404T1 (en) | 1999-02-15 |
EP0590431A1 (en) | 1994-04-06 |
JP2744879B2 (en) | 1998-04-28 |
CA2107246A1 (en) | 1994-03-31 |
DE69323374D1 (en) | 1999-03-18 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
CA2107246C (en) | Defibrillation patch electrode having conductor-free resilient zone for minimally invasive deployment | |
CA2109037C (en) | Implantable conformal coil patch electrode with multiple conductive elements for cardioversion and defibrillation | |
US5397342A (en) | Resilient structurally coupled and electrically independent electrodes | |
US4567900A (en) | Internal deployable defibrillator electrode | |
US4270549A (en) | Method for implanting cardiac electrodes | |
US4291707A (en) | Implantable cardiac defibrillating electrode | |
EP0280564B1 (en) | Implantable defribrillation electrodes | |
US4817608A (en) | Cardioverting transvenous catheter/patch electrode system and method for its use | |
EP0836509B1 (en) | Single-pass a-v lead for pacing with stimulation of right ventricular outflow tract | |
CA1309468C (en) | Cardioverting method and apparatus utilizing catheter and patch electrodes | |
US9002478B1 (en) | Passive fixation for epicardial lead | |
US4765341A (en) | Cardiac electrode with attachment fin | |
US8055355B2 (en) | System and assembly having conductive fixation features | |
US5405374A (en) | Transvenous defibrillation lead and method of use | |
JPH0458347B2 (en) | ||
US4972833A (en) | Epicardiac pacing lead | |
WO1982002664A1 (en) | Implantable cardiac defibrillating electrode | |
US5439484A (en) | Defibrillator employing transvenous and subcutaneous electrodes | |
WO2008024718A1 (en) | Epicardial lead | |
US20040106959A1 (en) | Implantable Medical Device with Multiple Electrode Lead | |
CA1173511A (en) | Method and apparatus for implanting cardiac electrode | |
CA1182532A (en) | Implantable cardiac defibrillating electrode | |
EP1284147A2 (en) | Preformed three-pole/four-pole lead for cardiac stimulation |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
EEER | Examination request | ||
MKLA | Lapsed |