CA2448376A1 - One piece header assembly for an implantable medical device - Google Patents
One piece header assembly for an implantable medical device Download PDFInfo
- Publication number
- CA2448376A1 CA2448376A1 CA002448376A CA2448376A CA2448376A1 CA 2448376 A1 CA2448376 A1 CA 2448376A1 CA 002448376 A CA002448376 A CA 002448376A CA 2448376 A CA2448376 A CA 2448376A CA 2448376 A1 CA2448376 A1 CA 2448376A1
- Authority
- CA
- Canada
- Prior art keywords
- medical device
- header assembly
- wire
- conductor
- feedthrough
- 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.)
- Abandoned
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/372—Arrangements in connection with the implantation of stimulators
- A61N1/375—Constructional arrangements, e.g. casings
- A61N1/3752—Details of casing-lead connections
Abstract
The present invention is directed to a header assembly mounted to a medical device for connecting to at least one conductor lead terminating at a target organ or portion of the body intending to be assisted. The header assembly comprises a body of polymeric material supporting at least one unitary conductor wire. The conductor wire connects between a feedthrough wire exiting the medical device and a terminal block into which the conductor lead plugs. Various structures are described for connecting the conductor wire to the feedthrough wire.
Description
37505.0230 ONE PIECE HEADER ASSEMBLY
FOR AN IMPLANTABLE MEDICAL DEVICE
CROSS REFERENCE TO RELATED APPLICATIONS
This application claims priority based on provisional applications Serial No_ 60/423,787, filed November 5, 2002, BACKGROUND OF THE INVENTION
1. Field of the Invention The invention relates to a one-piece header assembly for connecting an implantable medical device to a body organ assisted by the medical device. The header assembly includes terminal blocks electrically connected to the distal end of intermediate conductor wires supported in the header. The proximal end of the intermediate conductor wires comprise a quick connect structure for connecting to feedthrough wires or pins exiting the medical device. Electrical leads are plugged into the terminal blocks to establish continuity from the medical device to a tip of the electrical. leads inserted into a body tissue.
FOR AN IMPLANTABLE MEDICAL DEVICE
CROSS REFERENCE TO RELATED APPLICATIONS
This application claims priority based on provisional applications Serial No_ 60/423,787, filed November 5, 2002, BACKGROUND OF THE INVENTION
1. Field of the Invention The invention relates to a one-piece header assembly for connecting an implantable medical device to a body organ assisted by the medical device. The header assembly includes terminal blocks electrically connected to the distal end of intermediate conductor wires supported in the header. The proximal end of the intermediate conductor wires comprise a quick connect structure for connecting to feedthrough wires or pins exiting the medical device. Electrical leads are plugged into the terminal blocks to establish continuity from the medical device to a tip of the electrical. leads inserted into a body tissue.
2. Prior Art Implantable medical devices have feedthrough conductors in the form of pins or wires connected to the 37505.0230 internal components of the medical device. The feedthrough wires extend through a wall of the medical device housing and are electrica:Lly insulated therefrom by a ceramic-to-metal seal or a glass-to-metal seal.
Electrical continuity to a conductor lead attached to the body being assisted is established by connecting intermediate conductor wires supported by a polymeric header mounted on the medical device to the feedthrough wires and terminal blocks in the molded header. The terminal blocks then provide for plugging the conductor lead into the molded polymeric header. Examples of this type of header assembly are shown in U.S. Patent Nos.
4,254,775 to Langer, 4,262,6?3 to Kinney et al., 4,764,132 to Stutz, Jr., 5,282,841 to Szyszkowski and 5,336,246 to Dantanarayana. However, what is needed is a quick and reliable connection between the feedthrough wires from the medical device and the intermediate conductor wires supported by the molded header. The present invention connection structures are improvements over those shown by the prior art patents.
SUMMARY OF THE INVENTION
The present invention is, therefore, directed to a header assembly for a medical device. The header assembly provides electrical connection between feedthrough wires extending from inside the medical device to a conductor lead connected to the body organ or tissue being assisted.
Electrical continuity to a conductor lead attached to the body being assisted is established by connecting intermediate conductor wires supported by a polymeric header mounted on the medical device to the feedthrough wires and terminal blocks in the molded header. The terminal blocks then provide for plugging the conductor lead into the molded polymeric header. Examples of this type of header assembly are shown in U.S. Patent Nos.
4,254,775 to Langer, 4,262,6?3 to Kinney et al., 4,764,132 to Stutz, Jr., 5,282,841 to Szyszkowski and 5,336,246 to Dantanarayana. However, what is needed is a quick and reliable connection between the feedthrough wires from the medical device and the intermediate conductor wires supported by the molded header. The present invention connection structures are improvements over those shown by the prior art patents.
SUMMARY OF THE INVENTION
The present invention is, therefore, directed to a header assembly for a medical device. The header assembly provides electrical connection between feedthrough wires extending from inside the medical device to a conductor lead connected to the body organ or tissue being assisted.
37505.0230 Several different embodiments of header assemblies are described comprising structures for securing the feedthrough wires from the medical device to conductor wires in the molded header. The conductor wires are, in turn, connected to terminal blocks into which the lead wires from the body tissue are plugged into.
These features of the present invention will be apparent upon consideration of the following detailed description thereof presented in connection with the following drawings.
BRIEF DESCRIPTION OF THE DRAWINGS
Fig. 1 is an exploded view of a header assembly 10 mounted on an implantable medical device 18 according to the present invention.
Fig. 2 is a perspective view of the header assembly 10 shown in Fig. 1.
Fig. 3 is another perspective view of the header assembly shown in Fig. 1.
Fig. 4 is a cross-sectional view taken along line 4-4 of Fig. 2.
Fig. 5 is a cross-sectional view taken along line 5-5 of Fig. 4.
Fig. 6 is a perspective view of an alternate embodiment of an intermediate conductor lead 100.
These features of the present invention will be apparent upon consideration of the following detailed description thereof presented in connection with the following drawings.
BRIEF DESCRIPTION OF THE DRAWINGS
Fig. 1 is an exploded view of a header assembly 10 mounted on an implantable medical device 18 according to the present invention.
Fig. 2 is a perspective view of the header assembly 10 shown in Fig. 1.
Fig. 3 is another perspective view of the header assembly shown in Fig. 1.
Fig. 4 is a cross-sectional view taken along line 4-4 of Fig. 2.
Fig. 5 is a cross-sectional view taken along line 5-5 of Fig. 4.
Fig. 6 is a perspective view of an alternate embodiment of an intermediate conductor lead 100.
37505.0230 Fig. 7 is a partial cross-sectional view of the header 16 supporting a plurality of conductor leads 100, 106, 108 and 110.
Fig. 8 is a cross-sectional view taken along line 8-8 of Fig. 7.
Fig. 9 is a partial cross-sectional view of header 16 supporting a plurality of intermediate conductor wires 120, 132, 134 and 136 accordingly to another embodiment of the invention.
Fig. 10 is a cross-sectional. view of conductor wire 120 and its associated conductor block 122.
Fig. 10A illustrates an alternate embodiment of a conductor wire 121 having a unitary proximal end 121A
supporting a coil spring 128 in an inner annular groove 125 thereof.
Fig. 11 is a cross-sectional view taken along line 11-11 of Fig. 10.
Fig. 11A illustrates an alternate embodiment of an leaf spring 129 supported in an inner annular groove 126 provided at the proximal end of a conductor wire.
Fig. 12 is a perspective view of one embodiment of a bracket 142 for securing a polymeric header 140 to the medical device 22.
Figs. 13 and 14 are side and front elevational views, respectively, showing the header 140 being secured to the medical device 22.
37505.0230 Fig. 15 is a perspective view of another embodiment of a bracket 162 for securing a polymeric header 160 to the medical device 122.
Figs. 16 and 17 are side and front elevational views, respectively, showing the header 160 being secured to the medical device 22.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
Referring now to the drawings, Figs. 1 to 6 illustrate a header assembly 10 according to the present invention comprising two pairs of terminal blocks 12A, 12B
and 14A, 14B partially surrounded. by a header 16 comprising a body of molded polymeric material mounted on a support plate 18. The support plate 18, in turn, is mounted on the header portion 20 of an implantable medical device 22. The terminal block pairs 12A, 12B and 14A, 14B
each provide for connecting the lead 24 for a co-axial conductor wire from the medical device to a body tissue.
The implantable medical device 22 is exemplary of any one of a number of known assist devices such as cardiac defibrillators, cardiac pacemakers, drug pumps, neurostimulators, hearing assist devices, and the like.
The implantable medical device 22 comprises a housing 26 of a conductive material, such as of titanium or stainless steel. Preferably, the medical device housing 26 is comprised of mating clam shells in an overlapping or butt welded construction, as shown in U.S. Patent No.
37505.0230 6,613,474 to Frustaci et al., which is assigned to the assignee of the present invention and incorporated herein by reference. The housing 26 can also be of a deep drawn, prismatic and cylindrical design, as is well known to those skilled in the art.
The housing 26 is shown in an exemplary form comprising first and second planar major face walls 28 and 30 joined together by a sidewall 32 and the header 20.
The sidewall 32 curves from one end of the header 20 to the other end and is generally a:rcuate from face wall 28 to face wall 30. The preferred mating clam shells of housing 26 are hermetically sealed together, such as by laser or resistance welding, to provide an enclosure for the medical device including its control circuitry 34 and a power supply 36, such as a battery (the control circuitry and power supply are shown in dashed lines in Fig. 1). The power supply 36 is connected to the control circuitry 34 by electrical leads (not shown). There may also be a capacitor for a medical device such as a defibrillator.
The header 20 of housing 26 has a planar upper surface 38 providing at least four openings through which respective feedthrough wires 40, 42, 44, and 46 pass. The feedthrough wires extend from a distal end positioned inside the housing 26 connected to the control circuitry 34 to respective proximal ends spaced above the header upper surface 38. The feedthrough wires 40, 42, 44, and 46 are electrically insulated from the housing 26 by _ 7 _ 37505.0230 respective ceramic-to-metal seals or glass-to-metal seals (not shown), as are well known by those skilled in the art.
As shown in Fig. 3, the terminal block pairs 12A, 12B
and 14A, 14B are aligned in a co-axial relationship and encased in the polymeric material of the molded header 16.
The molded header 16 comprises spaced apart front and back walls 48 and 50 extending to a curved upper wall 52 and a generally planar bottom wall 54. The bottom wall 54 is supported on the upper surface 56 of support plate 18 and retained in place by encasing a peripheral undercut 58 of the support plate. In an alternate embodiment, the support plate 18 is replaced by a ring (not shown) having either an outer peripheral undercut or an inner peripheral undercut, or both.
Those skilled in the art will readily understand that the exact shape of the molded header is exemplary. In fact, the molded header can have a myriad of different shapes only limited by the design specifications of the associated medical device and its intended use.
Each terminal block 12A, 128, 14A, 14B has an internal cylindrically shaped bore. The terminal block pairs 12A, 12B and 14A, 14B have their internal bores aligned along the longitudinal axis of a respective bore 60, 62 leading into the polymeric header 16 from the curved upper wall 52. The structure of the bores 60, 62 will be described in detail with respect to the former 37505.0230 bore. However, it is understood that a similar structure exists for bore 62.
In that respect, the header assembly bore 60 has a first portion 60A of a first diameter sized to receive a distal portion 24A of the conductor lead 24, a second, intermediate portion 60B of a second, greater diameter sized to receive a proximal portion 24B of the lead and a third portion 60C of a still greater diameter than the intermediate portion. Frustoconically shaped portions lead from one bore portion to the next larger bore portion. The terminal blocks 12A, 12H have lead openings of diameters somewhat larger than the first and second bore portions 60A, 60B so that the conductor lead 24 is received therein in a tight fitting, electrically stable connection.
As shown in Fig. 4, each terminal block 12A, 12B, 14A
and 14B is connected to an intermediate conductor wire that provides electrical conductivity between the block and its associated feedthrough wires from the medical device. More specifically, intermediate conductor wire 64 is a unitary member having a distal end electrically secured, such as by welding, to the outer wall of terminal block 12A. This wire 64 has a bend along its length and leads to a proximal end 64A residing in an inlet 65 in the bottom wall 54 of the header 16. The intermediate conductor wire 64 has a generally circular cross-section perpendicular to its longitudinal axis except at its proximal end. There, the wire has a step 64A about _ g _ 37505.0230 halfway through its diameter. The step 64A provides a lap joint structure for securing the intermediate conductor wire 64 to feedthrough wire 40, as will be described in detail presently.
In a similar manner, terminal block 12B is electrically connected to the distal end of intermediate conductor wire 66. The proximal end of wire 66 residing in the inlet 65 has a step 66A. The step 66A provides a lap joint for securing the intermediate conductor wire 66 to feedthrough wire 42.
Terminal block 14A is electrically connected to the distal end of intermediate conductor wire 68. The proximal end of wire 68 has a step 68A residing in inlet 65 for securing the intermediate conductor wire to feedthrough wire 44.
Terminal block 14B is electrically connected to the distal end of intermediate conductor wire 70. The proximal end of wire 70 has a step 70A residing in inlet 65 for securing the intermediate conductor wire to feedthrough wire 46.
While header 16 is illustrated having two pairs of terminal blocks, this is for illustrative purposes only.
Those skilled in the art will realize that the header can have one pair of terminal blocks, or more than two pairs.
Also, the terminal blocks need not be provided in pairs.
Instead, a header bore can be in communication with only one terminal block, or with more Khan two aligned blocks.
37505.0230 Terminal blocks 12B and 14B are each provided with respective inner annular grooves 72 and 74. Respective collapsible coil springs 76, 78 are nested in the grooves 72, 74 to help ensure that the terminal blocks 12B, 14B
are electrically connected to the conductor leads 24 received in the bores 60, 62.
The front wall 48 of the molded header 16 is provided with an oval shaped raised land F30. A pair of passageways 82 and 84 enter the raised land 80 to communicate with the respective terminal blocks 12A, ~.4A. The passageways 82, 84 are aligned perpendicularly with the longitudinal axes of the bores 60, 62. Passageway 82 leads to a threaded aperture 86 (Figs. 1, 2 and 5) it terminal block 22A that receives a setscrew (not shown). The setscrew contacts the distal portion 24A of the conductor lead 24 to prevent loss of electrical contact between the lead and the terminal blocks 12A, 12B. Similarly, passageway 84 extends to a threaded aperture 88 in the sidewall of terminal block 14A that receives a setscrew (not shown) to maintain electrical continuity between the lead and the terminal blocks 14A, 14B.
The thusly described molded header 16 is mounted on the medical device 22 with the support plate 18 contacting the upper surface 38 of the header 20. The support plate 18 has an opening 18A (Figs. 1, 2 and 4) through which the feedthrough wires 40, 42, 44 and 46 extend. The support plate 18 and header 20 are both of_ a conductive metal and welding is typically used to join them together. fnlith the ., 11 .-37505.0230 molded header 16 secured to the medical device 22, the feedthrough wire 40 is of a length to overlap the step 64A
at the proximal end of intermediate conductor wire 64 residing in inlet 65. Welding t~.he feedthrough wire 40 to the step 64A of conductor wire 64 then makes electrical connection. In this manner, there are only two connections between the medical device and the terminal block. One is where the feedthrough wire 40 connects to the step 64A and the other is where the distal end of the intermediate conductor wire 64 connects to the terminal block 12A.
A similar electrical connection is made by welding feedthrough wire 42 to step 66A of conductor wire 66, feedthrough wire 44 to step 68A of conductor wire 68 and feedthrough wire 46 to step 70A of conductor wire 70. In this manner, electrical continuity is established between the control circuitry 34 of the medical device 22 and the terminal blocks 12A, 128, 14A and 14B through respective intermediate conductor wires 64, 66, 68 and 70.
Inlet 65 in the molded header 16 (Figs. 1 to 4) where the feedthrough wires 40, 42, 44 and 46 and the proximal ends 64A, 66A, 68A and 70A of the intermediate conductor wires are connected together is then back filled with a polymeric material. A suitable one is a silicon-based material. This prevents body fluids from coming into contact with these electrical connections.
In use, the medical device is positioned in a body, such as a human or animal, to assist a body function. A
37505.0230 suture opening 90 is provided in the molded header 16 to aid in securing the medical device 22 inside the body.
The physician then plugs a conductor lead 24 into each bore 60, 62 in molded header 16. The distal end (not shown? of the co-axial conductor opposite that of the lead 24 has already been positioned in a body tissue, such as a heart muscle, for transmitting physiological information to the medical device and for administering a medical theory as needed.
An example of this is in a cardiac defibrillator where the medical device may monitor the heart rate for extended periods of time. vJhen a potentially fatal irregular, rapid heartbeat known as tachyarrhythmia is detected, the defibrillator delivers an electrical shock to the heart. The electrical shock is transmitted from the control circuitry 34 through the feedthrough wires 40, 42, 44 and 46 and intermediate conductor wires 64, 66, 68 and 70. These conductors are electrically connected to the terminal blocks 12A, 12B, 14A and 14B into which the conductor leads 24 are plugged.
Figs. 6 to 8 show an alternate embodiment of an intermediate conductor wire 100 according to the present invention. Conductor wire 100 is useful in lieu of, or in combination with, the previously described conductor wires 64, 66, 68 and 70. For example, terminal blocks 12A and 12B could be connected to an intermediate terminal wire of the structure 64 and 66 while terminal blocks 14A and 14B
could be connected to intermediatEe conductor wire 100.
37505.0230 In any event, conductor wire 100 is preferably a unitary member having a circular cross-section perpendicular to its length extending from a distal end (not shown) electrically secured to a terminal block, for example block 12A, to an opposite proximal end 100A. The proximal end 100A of the conductor wire 100 resides in the inlet 65 of the molded header 16. The proximal end 100A
comprises a head 102 of a larger diameter than the remaining length of the wire 100. The head 102 is a cylindrically shaped portion of a length somewhat less than the depth of inlet 65. A bore 104 is provided in head 102 aligned along the longitudinal axis thereof.
Fig. 7 shows the molded polymeric header 16 supporting four conductor wires 100, 106, 108 and 110 corresponding to the feedthrough wires 40, 42, 44 and 46.
The feedthrough wires are received inside the bore 104 of head 102 of the conductor wires with the header 16 mounted on the medical device 22. The conductor wires and feedthrough wires are then joined together such as by welding. A silicon-based material (not shown) is used to backfill inlet 65 in molded header 16.
Figs. 9 to 11 show another embodiment of an intermediate conductor wire 120 according to the present invention. As with conductor wire 100, conductor wire 120 is useful in lieu of, or along with, the previously described conductor wires. Conductor wire 120 has a circular cross-section perpendicular to its length extending from a distal end (not shown) electrically 37505.0230 secured to a terminal block, for example block 12A, to an opposite proximal end 120A. The end 120A resides in the inlet 65 of the molded polymeric header 16 and is received in a bore in a connector block 122. The conductor wire 120 and connector block 122 are preferably welded together. A coaxial bore 124 extends part way into the length of conductor block 122. An annular groove 126 provided in the sidewall of bore 124 has an annular coil spring 128 nested therein.
Fig. 9 shows the molded header 16 supporting four conductor wires.122, 130, 132, and 134 corresponding to the feedthrough wires 40, 42, 44 and 46. The feedthrough wires are received inside the bore 124 of the conductor block 122 of each of the conductor wires with the header 16 mounted on the medical device 22. There is no need to join the conductor wires and feedthrough wires by welding.
Instead, the coil spring 128 provided sufficient conductivity between the feedthrough wires and the connector block 122 welded to the end 120A of the intermediate connector wire 120. A silicon-based material (not shown) is used to backfill the inlet 65 in the molded header 16.
As shown in Fig. 10A, it is further within the scope of the present invention that the conductor wire 120 and connector block 122 are unitary. Conductor wire 121 has a circular cross-section perpendicular to its length extending from a distal end (not shown) electrically secured to a terminal block, for example block 12A, to an 37505.0230 opposite proximal head 121A. The proximal head 121A of conductor wire 121 resides in the inlet 65 of the molded polymeric header 16 and includes a coaxial bore 123 extending part ways into its length. An annular groove 125 provided in the sidewall of bore 123 has a coil spring 128 nested therein. In all other respects, conductor wire 121 functions in a similar manner as the previously described wire 120 and connector block 122.
It is also within the scope of the present invention that the spring need not be of a coil structure. As shown in Fig. 11A, the annular groove 126 provided in the sidewall of bore 124 supports an annular leaf spring 129 nested therein.
Figs. 12 to 14 illustrate an alternate embodiment of a structure for securing a polymeric header 140 to the medical device 22. Polymeric header 140 is similar to the previously described header 16 except it is not molded to an undercut of a support plate. Instead, the header 20 of the medical device supports an L-shaped bracket 142, preferably of a metal such as titanium or stainless steel, having an upstanding wall 142A provided with an elongated slot 144. The longitudinal axis of slot 144 is parallel to the planar upper surface 56 of the medical device header 20. The bottom wall 54A of header 140 is provided with an inlet 146 that matches the shape of bracket 142.
A lateral inlet 148 is provided in the sidewall 150 of header 140 and intersects with inlet 146. When the molded header 140 is mounted on the medical device 22, the 37505.0230 bracket 142 is received in the inlet 146. In this position, the lateral inlet 148 is aligned with slot 144.
As shown in Fig. 13, a wedge 152, preferably of a metal such as that of the bracket 142, is moved into the lateral inlet 148 and bracket slot 144 to pin or secure the header and medical device together. The wedge can also be of a polymeric material.
Figs. 15 to 17 illustrate an alternate embodiment of a structure for securing a polymeric header 160, similar to the previously described head<~r 140, to the medical device 22. The medical device header 20 supports a U-shaped bracket 162, preferably of a metal such as titanium or stainless steel, having a pair of upstanding sidewalls 162A and 1628, each provided with an elongated slot 164.
The longitudinal axes of the slogs 164 are parallel to the planar upper surface 56 of the medical device header 20.
The bottom wall 548 of the molded header 160 is provided with an inlet 166 that matches the shape of bracket 162.
A lateral inlet 168 is provided in the sidewall 170 of header 160 and intersects with inlet 164. When the header 160 is mounted on the medical device 22, the bracket 162 is received in the inlet 166. In this position, the lateral inlet 168 is aligned with slots 164. As shown in Fig. 16, a metal or polymeric wedge 172 is moved into the lateral inlet 168 and bracket slots 164 to secure the header 160 and medical device 22 together.
Now, it is therefore apparent that the present invention accomplishes its intended objects. While 37505.0230 embodiments of the present invention have been described in detail, that is for the purpose of illustration, not limitation.
Fig. 8 is a cross-sectional view taken along line 8-8 of Fig. 7.
Fig. 9 is a partial cross-sectional view of header 16 supporting a plurality of intermediate conductor wires 120, 132, 134 and 136 accordingly to another embodiment of the invention.
Fig. 10 is a cross-sectional. view of conductor wire 120 and its associated conductor block 122.
Fig. 10A illustrates an alternate embodiment of a conductor wire 121 having a unitary proximal end 121A
supporting a coil spring 128 in an inner annular groove 125 thereof.
Fig. 11 is a cross-sectional view taken along line 11-11 of Fig. 10.
Fig. 11A illustrates an alternate embodiment of an leaf spring 129 supported in an inner annular groove 126 provided at the proximal end of a conductor wire.
Fig. 12 is a perspective view of one embodiment of a bracket 142 for securing a polymeric header 140 to the medical device 22.
Figs. 13 and 14 are side and front elevational views, respectively, showing the header 140 being secured to the medical device 22.
37505.0230 Fig. 15 is a perspective view of another embodiment of a bracket 162 for securing a polymeric header 160 to the medical device 122.
Figs. 16 and 17 are side and front elevational views, respectively, showing the header 160 being secured to the medical device 22.
DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS
Referring now to the drawings, Figs. 1 to 6 illustrate a header assembly 10 according to the present invention comprising two pairs of terminal blocks 12A, 12B
and 14A, 14B partially surrounded. by a header 16 comprising a body of molded polymeric material mounted on a support plate 18. The support plate 18, in turn, is mounted on the header portion 20 of an implantable medical device 22. The terminal block pairs 12A, 12B and 14A, 14B
each provide for connecting the lead 24 for a co-axial conductor wire from the medical device to a body tissue.
The implantable medical device 22 is exemplary of any one of a number of known assist devices such as cardiac defibrillators, cardiac pacemakers, drug pumps, neurostimulators, hearing assist devices, and the like.
The implantable medical device 22 comprises a housing 26 of a conductive material, such as of titanium or stainless steel. Preferably, the medical device housing 26 is comprised of mating clam shells in an overlapping or butt welded construction, as shown in U.S. Patent No.
37505.0230 6,613,474 to Frustaci et al., which is assigned to the assignee of the present invention and incorporated herein by reference. The housing 26 can also be of a deep drawn, prismatic and cylindrical design, as is well known to those skilled in the art.
The housing 26 is shown in an exemplary form comprising first and second planar major face walls 28 and 30 joined together by a sidewall 32 and the header 20.
The sidewall 32 curves from one end of the header 20 to the other end and is generally a:rcuate from face wall 28 to face wall 30. The preferred mating clam shells of housing 26 are hermetically sealed together, such as by laser or resistance welding, to provide an enclosure for the medical device including its control circuitry 34 and a power supply 36, such as a battery (the control circuitry and power supply are shown in dashed lines in Fig. 1). The power supply 36 is connected to the control circuitry 34 by electrical leads (not shown). There may also be a capacitor for a medical device such as a defibrillator.
The header 20 of housing 26 has a planar upper surface 38 providing at least four openings through which respective feedthrough wires 40, 42, 44, and 46 pass. The feedthrough wires extend from a distal end positioned inside the housing 26 connected to the control circuitry 34 to respective proximal ends spaced above the header upper surface 38. The feedthrough wires 40, 42, 44, and 46 are electrically insulated from the housing 26 by _ 7 _ 37505.0230 respective ceramic-to-metal seals or glass-to-metal seals (not shown), as are well known by those skilled in the art.
As shown in Fig. 3, the terminal block pairs 12A, 12B
and 14A, 14B are aligned in a co-axial relationship and encased in the polymeric material of the molded header 16.
The molded header 16 comprises spaced apart front and back walls 48 and 50 extending to a curved upper wall 52 and a generally planar bottom wall 54. The bottom wall 54 is supported on the upper surface 56 of support plate 18 and retained in place by encasing a peripheral undercut 58 of the support plate. In an alternate embodiment, the support plate 18 is replaced by a ring (not shown) having either an outer peripheral undercut or an inner peripheral undercut, or both.
Those skilled in the art will readily understand that the exact shape of the molded header is exemplary. In fact, the molded header can have a myriad of different shapes only limited by the design specifications of the associated medical device and its intended use.
Each terminal block 12A, 128, 14A, 14B has an internal cylindrically shaped bore. The terminal block pairs 12A, 12B and 14A, 14B have their internal bores aligned along the longitudinal axis of a respective bore 60, 62 leading into the polymeric header 16 from the curved upper wall 52. The structure of the bores 60, 62 will be described in detail with respect to the former 37505.0230 bore. However, it is understood that a similar structure exists for bore 62.
In that respect, the header assembly bore 60 has a first portion 60A of a first diameter sized to receive a distal portion 24A of the conductor lead 24, a second, intermediate portion 60B of a second, greater diameter sized to receive a proximal portion 24B of the lead and a third portion 60C of a still greater diameter than the intermediate portion. Frustoconically shaped portions lead from one bore portion to the next larger bore portion. The terminal blocks 12A, 12H have lead openings of diameters somewhat larger than the first and second bore portions 60A, 60B so that the conductor lead 24 is received therein in a tight fitting, electrically stable connection.
As shown in Fig. 4, each terminal block 12A, 12B, 14A
and 14B is connected to an intermediate conductor wire that provides electrical conductivity between the block and its associated feedthrough wires from the medical device. More specifically, intermediate conductor wire 64 is a unitary member having a distal end electrically secured, such as by welding, to the outer wall of terminal block 12A. This wire 64 has a bend along its length and leads to a proximal end 64A residing in an inlet 65 in the bottom wall 54 of the header 16. The intermediate conductor wire 64 has a generally circular cross-section perpendicular to its longitudinal axis except at its proximal end. There, the wire has a step 64A about _ g _ 37505.0230 halfway through its diameter. The step 64A provides a lap joint structure for securing the intermediate conductor wire 64 to feedthrough wire 40, as will be described in detail presently.
In a similar manner, terminal block 12B is electrically connected to the distal end of intermediate conductor wire 66. The proximal end of wire 66 residing in the inlet 65 has a step 66A. The step 66A provides a lap joint for securing the intermediate conductor wire 66 to feedthrough wire 42.
Terminal block 14A is electrically connected to the distal end of intermediate conductor wire 68. The proximal end of wire 68 has a step 68A residing in inlet 65 for securing the intermediate conductor wire to feedthrough wire 44.
Terminal block 14B is electrically connected to the distal end of intermediate conductor wire 70. The proximal end of wire 70 has a step 70A residing in inlet 65 for securing the intermediate conductor wire to feedthrough wire 46.
While header 16 is illustrated having two pairs of terminal blocks, this is for illustrative purposes only.
Those skilled in the art will realize that the header can have one pair of terminal blocks, or more than two pairs.
Also, the terminal blocks need not be provided in pairs.
Instead, a header bore can be in communication with only one terminal block, or with more Khan two aligned blocks.
37505.0230 Terminal blocks 12B and 14B are each provided with respective inner annular grooves 72 and 74. Respective collapsible coil springs 76, 78 are nested in the grooves 72, 74 to help ensure that the terminal blocks 12B, 14B
are electrically connected to the conductor leads 24 received in the bores 60, 62.
The front wall 48 of the molded header 16 is provided with an oval shaped raised land F30. A pair of passageways 82 and 84 enter the raised land 80 to communicate with the respective terminal blocks 12A, ~.4A. The passageways 82, 84 are aligned perpendicularly with the longitudinal axes of the bores 60, 62. Passageway 82 leads to a threaded aperture 86 (Figs. 1, 2 and 5) it terminal block 22A that receives a setscrew (not shown). The setscrew contacts the distal portion 24A of the conductor lead 24 to prevent loss of electrical contact between the lead and the terminal blocks 12A, 12B. Similarly, passageway 84 extends to a threaded aperture 88 in the sidewall of terminal block 14A that receives a setscrew (not shown) to maintain electrical continuity between the lead and the terminal blocks 14A, 14B.
The thusly described molded header 16 is mounted on the medical device 22 with the support plate 18 contacting the upper surface 38 of the header 20. The support plate 18 has an opening 18A (Figs. 1, 2 and 4) through which the feedthrough wires 40, 42, 44 and 46 extend. The support plate 18 and header 20 are both of_ a conductive metal and welding is typically used to join them together. fnlith the ., 11 .-37505.0230 molded header 16 secured to the medical device 22, the feedthrough wire 40 is of a length to overlap the step 64A
at the proximal end of intermediate conductor wire 64 residing in inlet 65. Welding t~.he feedthrough wire 40 to the step 64A of conductor wire 64 then makes electrical connection. In this manner, there are only two connections between the medical device and the terminal block. One is where the feedthrough wire 40 connects to the step 64A and the other is where the distal end of the intermediate conductor wire 64 connects to the terminal block 12A.
A similar electrical connection is made by welding feedthrough wire 42 to step 66A of conductor wire 66, feedthrough wire 44 to step 68A of conductor wire 68 and feedthrough wire 46 to step 70A of conductor wire 70. In this manner, electrical continuity is established between the control circuitry 34 of the medical device 22 and the terminal blocks 12A, 128, 14A and 14B through respective intermediate conductor wires 64, 66, 68 and 70.
Inlet 65 in the molded header 16 (Figs. 1 to 4) where the feedthrough wires 40, 42, 44 and 46 and the proximal ends 64A, 66A, 68A and 70A of the intermediate conductor wires are connected together is then back filled with a polymeric material. A suitable one is a silicon-based material. This prevents body fluids from coming into contact with these electrical connections.
In use, the medical device is positioned in a body, such as a human or animal, to assist a body function. A
37505.0230 suture opening 90 is provided in the molded header 16 to aid in securing the medical device 22 inside the body.
The physician then plugs a conductor lead 24 into each bore 60, 62 in molded header 16. The distal end (not shown? of the co-axial conductor opposite that of the lead 24 has already been positioned in a body tissue, such as a heart muscle, for transmitting physiological information to the medical device and for administering a medical theory as needed.
An example of this is in a cardiac defibrillator where the medical device may monitor the heart rate for extended periods of time. vJhen a potentially fatal irregular, rapid heartbeat known as tachyarrhythmia is detected, the defibrillator delivers an electrical shock to the heart. The electrical shock is transmitted from the control circuitry 34 through the feedthrough wires 40, 42, 44 and 46 and intermediate conductor wires 64, 66, 68 and 70. These conductors are electrically connected to the terminal blocks 12A, 12B, 14A and 14B into which the conductor leads 24 are plugged.
Figs. 6 to 8 show an alternate embodiment of an intermediate conductor wire 100 according to the present invention. Conductor wire 100 is useful in lieu of, or in combination with, the previously described conductor wires 64, 66, 68 and 70. For example, terminal blocks 12A and 12B could be connected to an intermediate terminal wire of the structure 64 and 66 while terminal blocks 14A and 14B
could be connected to intermediatEe conductor wire 100.
37505.0230 In any event, conductor wire 100 is preferably a unitary member having a circular cross-section perpendicular to its length extending from a distal end (not shown) electrically secured to a terminal block, for example block 12A, to an opposite proximal end 100A. The proximal end 100A of the conductor wire 100 resides in the inlet 65 of the molded header 16. The proximal end 100A
comprises a head 102 of a larger diameter than the remaining length of the wire 100. The head 102 is a cylindrically shaped portion of a length somewhat less than the depth of inlet 65. A bore 104 is provided in head 102 aligned along the longitudinal axis thereof.
Fig. 7 shows the molded polymeric header 16 supporting four conductor wires 100, 106, 108 and 110 corresponding to the feedthrough wires 40, 42, 44 and 46.
The feedthrough wires are received inside the bore 104 of head 102 of the conductor wires with the header 16 mounted on the medical device 22. The conductor wires and feedthrough wires are then joined together such as by welding. A silicon-based material (not shown) is used to backfill inlet 65 in molded header 16.
Figs. 9 to 11 show another embodiment of an intermediate conductor wire 120 according to the present invention. As with conductor wire 100, conductor wire 120 is useful in lieu of, or along with, the previously described conductor wires. Conductor wire 120 has a circular cross-section perpendicular to its length extending from a distal end (not shown) electrically 37505.0230 secured to a terminal block, for example block 12A, to an opposite proximal end 120A. The end 120A resides in the inlet 65 of the molded polymeric header 16 and is received in a bore in a connector block 122. The conductor wire 120 and connector block 122 are preferably welded together. A coaxial bore 124 extends part way into the length of conductor block 122. An annular groove 126 provided in the sidewall of bore 124 has an annular coil spring 128 nested therein.
Fig. 9 shows the molded header 16 supporting four conductor wires.122, 130, 132, and 134 corresponding to the feedthrough wires 40, 42, 44 and 46. The feedthrough wires are received inside the bore 124 of the conductor block 122 of each of the conductor wires with the header 16 mounted on the medical device 22. There is no need to join the conductor wires and feedthrough wires by welding.
Instead, the coil spring 128 provided sufficient conductivity between the feedthrough wires and the connector block 122 welded to the end 120A of the intermediate connector wire 120. A silicon-based material (not shown) is used to backfill the inlet 65 in the molded header 16.
As shown in Fig. 10A, it is further within the scope of the present invention that the conductor wire 120 and connector block 122 are unitary. Conductor wire 121 has a circular cross-section perpendicular to its length extending from a distal end (not shown) electrically secured to a terminal block, for example block 12A, to an 37505.0230 opposite proximal head 121A. The proximal head 121A of conductor wire 121 resides in the inlet 65 of the molded polymeric header 16 and includes a coaxial bore 123 extending part ways into its length. An annular groove 125 provided in the sidewall of bore 123 has a coil spring 128 nested therein. In all other respects, conductor wire 121 functions in a similar manner as the previously described wire 120 and connector block 122.
It is also within the scope of the present invention that the spring need not be of a coil structure. As shown in Fig. 11A, the annular groove 126 provided in the sidewall of bore 124 supports an annular leaf spring 129 nested therein.
Figs. 12 to 14 illustrate an alternate embodiment of a structure for securing a polymeric header 140 to the medical device 22. Polymeric header 140 is similar to the previously described header 16 except it is not molded to an undercut of a support plate. Instead, the header 20 of the medical device supports an L-shaped bracket 142, preferably of a metal such as titanium or stainless steel, having an upstanding wall 142A provided with an elongated slot 144. The longitudinal axis of slot 144 is parallel to the planar upper surface 56 of the medical device header 20. The bottom wall 54A of header 140 is provided with an inlet 146 that matches the shape of bracket 142.
A lateral inlet 148 is provided in the sidewall 150 of header 140 and intersects with inlet 146. When the molded header 140 is mounted on the medical device 22, the 37505.0230 bracket 142 is received in the inlet 146. In this position, the lateral inlet 148 is aligned with slot 144.
As shown in Fig. 13, a wedge 152, preferably of a metal such as that of the bracket 142, is moved into the lateral inlet 148 and bracket slot 144 to pin or secure the header and medical device together. The wedge can also be of a polymeric material.
Figs. 15 to 17 illustrate an alternate embodiment of a structure for securing a polymeric header 160, similar to the previously described head<~r 140, to the medical device 22. The medical device header 20 supports a U-shaped bracket 162, preferably of a metal such as titanium or stainless steel, having a pair of upstanding sidewalls 162A and 1628, each provided with an elongated slot 164.
The longitudinal axes of the slogs 164 are parallel to the planar upper surface 56 of the medical device header 20.
The bottom wall 548 of the molded header 160 is provided with an inlet 166 that matches the shape of bracket 162.
A lateral inlet 168 is provided in the sidewall 170 of header 160 and intersects with inlet 164. When the header 160 is mounted on the medical device 22, the bracket 162 is received in the inlet 166. In this position, the lateral inlet 168 is aligned with slots 164. As shown in Fig. 16, a metal or polymeric wedge 172 is moved into the lateral inlet 168 and bracket slots 164 to secure the header 160 and medical device 22 together.
Now, it is therefore apparent that the present invention accomplishes its intended objects. While 37505.0230 embodiments of the present invention have been described in detail, that is for the purpose of illustration, not limitation.
Claims (23)
1. A header assembly for connecting an implantable medical device to a conductor lead terminating at a body organ intended to be assisted by the medical device comprising a housing containing control circuitry, at least one electrical energy storage device, and at least one feedthrough wire extending from the control circuitry and through a wall of the housing, the header assembly comprising:
a) a body mounted on the housing for the medical device;
b) at least one terminal supported by the polymeric body, wherein the terminal is directly connectable to the conductor lead; and c) a unitary intermediate conductor supported by the body, the intermediate conductor having a distal end connected to the terminal and a proximal end directly connected to the feedthrough wire.
a) a body mounted on the housing for the medical device;
b) at least one terminal supported by the polymeric body, wherein the terminal is directly connectable to the conductor lead; and c) a unitary intermediate conductor supported by the body, the intermediate conductor having a distal end connected to the terminal and a proximal end directly connected to the feedthrough wire.
2. The header assembly of claim 1 wherein the proximal end of the intermediate conductor wire comprises a step that is securable to the feedthrough wire in a lap joint construction.
3. The header assembly of claim 1 wherein the proximal end of the intermediate conductor wire comprises an enlarged head having a bore into which the feedthrough wire is receivable and connectable.
4. The header assembly of claim 3 wherein the enlarged head comprises a bore and a groove in communication with the bore, and wherein a spring is nested in the groove so that when the feedthrough wire is received in the bore, the spring contacts the feedthrough wire.
5. The header assembly of claim 4 wherein the groove is an annular groove supporting an annular spring that surrounds the feedthrough wire.
6. The header assembly of claim 4 wherein the spring is a leaf spring.
7. The header assembly of claim 1 wherein the body is of a polymeric material.
8. The header assembly of claim 1 wherein the body includes a first inlet that receives a bracket secured to the housing and a second inlet and wherein with the bracket received in the first inlet, a wedge is receivable in the second inlet and a bracket inlet to secure the header assembly to the medical device.
9. The header assembly of claim 8 wherein the bracket is either L-shaped or U-shaped.
10. The header assembly of claim 1 wherein the housing for the medical device comprises mating first and second clam shells.
11. The header assembly of claim 1 wherein the medical device is selected from the group consisting of a hearing assist device, neurostimulator, cardiac pacemaker, drug pump and cardiac defibrillator.
12. A header assembly for connecting an implantable medical device to a conductor lead terminating at a body organ intended to be assisted by the medical device comprising a housing containing control circuitry, at least one electrical energy storage device, and at least one feedthrough wire extending from the control circuitry and through a wall of the housing, the header assembly comprising:
a) a body mounted on the housing for the medical device;
b) at least one terminal supported by the polymeric body, wherein the terminal is directly connectable to the conductor lead; and c) an intermediate conductor supported by the body, the intermediate conductor having a distal end connected to the terminal and a proximal end directly connected to the feedthrough wire.
a) a body mounted on the housing for the medical device;
b) at least one terminal supported by the polymeric body, wherein the terminal is directly connectable to the conductor lead; and c) an intermediate conductor supported by the body, the intermediate conductor having a distal end connected to the terminal and a proximal end directly connected to the feedthrough wire.
13. The header assembly of claim 12 wherein the proximal end of the intermediate conductor wire connects to an enlarged head comprising a bore and a groove in communication with the bore, and wherein a spring is nested in the groove so that when the feedthrough wire is received in the bore, the spring contacts the feedthrough wire.
14. The header assembly of claim 12 wherein the groove is an annular groove supporting an annular spring that surround the feedthrough wire.
15. The header assembly of claim 12 wherein the spring is a leaf spring.
16. A method for connecting an implantable medical device to a conductor terminating at a body organ intended to be assisted by the medical device, comprising the steps of:
a) providing the medical device having a housing containing control circuitry, at least one electrical energy storage device and at least one feedthrough wire extending from the control circuitry through a wall of the housing to a distal end located outside the housing;
b) providing a body supporting at least one terminal and at least one unitary intermediate conductor, wherein the intermediate conductor has a distal end connected to the terminal and a proximal end;
c) mounting the body on the medical device with the proximal end of the feedthrough wire disposed in an overlapping relationship with at least a portion of the intermediate conductor; and d) securing the proximal end of the feedthrough wire to the intermediate conductor.
a) providing the medical device having a housing containing control circuitry, at least one electrical energy storage device and at least one feedthrough wire extending from the control circuitry through a wall of the housing to a distal end located outside the housing;
b) providing a body supporting at least one terminal and at least one unitary intermediate conductor, wherein the intermediate conductor has a distal end connected to the terminal and a proximal end;
c) mounting the body on the medical device with the proximal end of the feedthrough wire disposed in an overlapping relationship with at least a portion of the intermediate conductor; and d) securing the proximal end of the feedthrough wire to the intermediate conductor.
17. The method of claim 16 wherein the proximal end of the intermediate conductor wire comprises a step and including the step of securing the feedthrough wire to the conductor wire in a lap joint construction.
18. The method of claim 16 wherein the proximal end of the intermediate conductor wire comprises an enlarged head having a bore into which the feedthrough wire is receivable and connectable.
19. The method of claim 18 wherein the bore in the enlarged head comprises a groove supporting a spring, and including the step of mounting the header assembly on the medical device with the feedthrough wire received in the bore and the spring contacting the feedthrough wire.
20. The method of claim 19 wherein the groove is an annular groove supporting an annular spring surrounding the feedthrough wire.
21. The method of claim 19 wherein the spring is a leaf spring.
22. The method of claim 16 including providing the body of a polymeric material.
23. The method of claim 16 including providing the body comprising a first inlet that receives a bracket secured to the housing and a second inlet and including the step of mounting the header assembly on the medical device with the bracket received in the first inlet and moving a wedge into the second inlet and a bracket inlet thereby securing the header assembly to the medical device.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US42378702P | 2002-11-05 | 2002-11-05 | |
| US60/423,787 | 2002-11-05 |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA2448376A1 true CA2448376A1 (en) | 2004-05-05 |
Family
ID=32108169
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002448376A Abandoned CA2448376A1 (en) | 2002-11-05 | 2003-11-05 | One piece header assembly for an implantable medical device |
Country Status (4)
| Country | Link |
|---|---|
| US (1) | US7167749B2 (en) |
| EP (1) | EP1417986A1 (en) |
| JP (1) | JP2004283550A (en) |
| CA (1) | CA2448376A1 (en) |
Families Citing this family (74)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP4015934B2 (en) * | 2002-04-18 | 2007-11-28 | 株式会社東芝 | Video coding method and apparatus |
| US7110827B2 (en) * | 2003-04-25 | 2006-09-19 | Medtronic, Inc. | Electrical connectors for medical lead having weld-less wiring connection |
| US7647111B2 (en) * | 2003-07-31 | 2010-01-12 | Medtronic, Inc. | Connector assembly for connecting a lead and an implantable medical device |
| US7769458B2 (en) * | 2003-07-31 | 2010-08-03 | Medtronic, Inc. | Small format connector clip of an implantable medical device |
| US20050027325A1 (en) * | 2003-07-31 | 2005-02-03 | Jay Lahti | Connector assembly for connecting a lead and an implantable medical device |
| US20060210131A1 (en) * | 2005-03-15 | 2006-09-21 | Wheeler Frederick W Jr | Tomographic computer aided diagnosis (CAD) with multiple reconstructions |
| US20060224208A1 (en) * | 2005-04-05 | 2006-10-05 | Bal Seal Engineering Co., Inc. | Medical electronics electrical implantable medical devices |
| US7567842B1 (en) * | 2005-09-29 | 2009-07-28 | Advanced Neuromodulation Systems, Inc. | Housing providing an electrical stimulation lead contact in an implantable stimulation device |
| EP1928547B1 (en) * | 2005-09-29 | 2011-05-25 | St. Jude Medical AB | Implantable medical device with interweldable housing and header |
| US7682202B2 (en) * | 2005-10-28 | 2010-03-23 | Cardiac Pacemakers, Inc. | Connector assembly for implantable device |
| US7413482B2 (en) * | 2005-11-17 | 2008-08-19 | Medtronic, Inc. | Method for forming a connector assembly for use with an implantable medical device |
| DE102006003224A1 (en) * | 2005-12-08 | 2007-06-14 | Biotronik Crm Patent Ag | Housing for a medical implant |
| DE102006003223A1 (en) * | 2005-12-08 | 2007-06-14 | Biotronik Crm Patent Ag | Housing for a medical implant |
| US7654843B2 (en) * | 2006-02-28 | 2010-02-02 | Medtronic, Inc. | Connector assembly with internal seals and manufacturing method |
| US7489968B1 (en) | 2006-04-07 | 2009-02-10 | Pacesetter, Inc. | Pre-molded header with universal tip-to-tip feedthru adaptor |
| US7583999B2 (en) * | 2006-07-31 | 2009-09-01 | Cranial Medical Systems, Inc. | Multi-channel connector for brain stimulation system |
| US20080103572A1 (en) | 2006-10-31 | 2008-05-01 | Medtronic, Inc. | Implantable medical lead with threaded fixation |
| US7502217B2 (en) * | 2007-02-16 | 2009-03-10 | Medtronic, Inc. | Filtering capacitor feedthrough assembly |
| US8233986B2 (en) * | 2007-07-12 | 2012-07-31 | Medtronic, Inc. | Connector header for implantable medical device |
| US8108045B2 (en) | 2007-10-29 | 2012-01-31 | Cretex Orthopaedics, Inc. | Set screw-less pacemaker header with lead lock system |
| US8065009B2 (en) * | 2008-01-25 | 2011-11-22 | Greatbatch Ltd. | Header over-molded on a feedthrough assembly for an implantable device |
| US7563142B1 (en) * | 2008-04-30 | 2009-07-21 | Medtronic, Inc. | Medical device packaging systems including electrical interfaces |
| US8346362B2 (en) | 2008-08-13 | 2013-01-01 | Greatbatch Ltd. | Molded header connected to a medical device by lateral deformation of a sleeve/feedthrough pin sub-assembly |
| US9095728B2 (en) | 2008-09-05 | 2015-08-04 | Medtronic, Inc. | Electrical contact for implantable medical device |
| US8096838B2 (en) | 2009-03-11 | 2012-01-17 | Bal Seal Engineering, Inc. | Header assembly for implantable medical devices |
| US8032221B2 (en) * | 2009-03-24 | 2011-10-04 | Medtronic, Inc. | Sealing setscrew |
| US8190260B2 (en) * | 2009-03-24 | 2012-05-29 | Medtronic, Inc. | Lead retention and sealing device |
| US20100249871A1 (en) * | 2009-03-24 | 2010-09-30 | Medtronic, Inc. | Full Visibility Lead Retention |
| US20110015694A1 (en) * | 2009-07-16 | 2011-01-20 | Pacesetter, Inc. | Prefabricated header for hermetically sealed device |
| EP2461867B1 (en) | 2009-08-05 | 2015-10-07 | Medtronic, Inc | Connector and contact assemblies for medical devices |
| US9403022B2 (en) * | 2010-01-29 | 2016-08-02 | Medtronic, Inc. | Header assembly for implantable medical device |
| US8386047B2 (en) * | 2010-07-15 | 2013-02-26 | Advanced Bionics | Implantable hermetic feedthrough |
| US8552311B2 (en) | 2010-07-15 | 2013-10-08 | Advanced Bionics | Electrical feedthrough assembly |
| EP2608844B1 (en) | 2010-08-25 | 2014-10-08 | Cardiac Pacemakers, Inc. | Apparatus and method for attaching a header to a housing of an implantable device |
| US11211741B2 (en) | 2011-06-03 | 2021-12-28 | Greatbatch Ltd. | Removable terminal pin connector for an active electronics circuit board for use in an implantable medical device |
| US8593816B2 (en) | 2011-09-21 | 2013-11-26 | Medtronic, Inc. | Compact connector assembly for implantable medical device |
| US20130110204A1 (en) * | 2011-10-26 | 2013-05-02 | Pacesetter, Inc. | Spring connector for implantable medical device |
| EP2773423B1 (en) | 2011-11-04 | 2024-01-10 | Nevro Corporation | Medical device communication and charding assemblies for use with implantable signal generators |
| US9227076B2 (en) * | 2011-11-04 | 2016-01-05 | Nevro Corporation | Molded headers for implantable signal generators, and associated systems and methods |
| US9011169B2 (en) | 2012-03-21 | 2015-04-21 | Bal Seal Engineering, Inc. | Connectors with electrical or signal carrying capabilities and related methods |
| US8628348B2 (en) * | 2012-05-17 | 2014-01-14 | Medtronic, Inc. | Connector module assemblies, methods, and components for implantable medical electrical devices |
| CA2882974C (en) | 2012-08-31 | 2018-10-23 | Alfred E. Mann Foundation For Scientific Research | Feedback controlled coil driver for inductive power transfer |
| US9209544B2 (en) * | 2013-01-31 | 2015-12-08 | Heraeus Precious Metals Gmbh & Co. Kg | Lead connector with distal frame and method of manufacture |
| US9044614B2 (en) | 2013-03-15 | 2015-06-02 | Alfred E. Mann Foundation For Scientific Research | High voltage monitoring successive approximation analog to digital converter |
| AU2014232252B2 (en) | 2013-03-15 | 2018-01-18 | Alfred E. Mann Foundation For Scientific Research | Current sensing multiple output current stimulators with fast turn on time |
| CN104602760B (en) | 2013-05-03 | 2017-11-07 | 艾尔弗雷德·E·曼科学研究基金会 | High reliability wire for embedded type device is welded |
| EP2991726B1 (en) | 2013-05-03 | 2018-07-25 | Alfred E. Mann Foundation for Scientific Research | Multi-branch stimulation electrode for subcutaneous field stimulation |
| CA2910984A1 (en) | 2013-05-03 | 2014-11-06 | Alfred E. Mann Foundation For Scientific Research | Implant recharger handshaking system and method |
| US9780596B2 (en) | 2013-07-29 | 2017-10-03 | Alfred E. Mann Foundation For Scientific Research | Microprocessor controlled class E driver |
| CA2919525C (en) | 2013-07-29 | 2021-07-20 | Alfred E. Mann Foundation For Scientific Research | High efficiency magnetic link for implantable devices |
| US9409020B2 (en) | 2014-05-20 | 2016-08-09 | Nevro Corporation | Implanted pulse generators with reduced power consumption via signal strength/duration characteristics, and associated systems and methods |
| CN107073257B (en) | 2014-08-15 | 2020-04-10 | 艾克索尼克斯调制技术股份有限公司 | EMG lead positioning and stimulation titration in a neurostimulation system for treating overactive bladder |
| CA2958197C (en) | 2014-08-15 | 2023-09-26 | Axonics Modulation Technologies, Inc. | External pulse generator device and associated methods for trial nerve stimulation |
| EP3180075A4 (en) | 2014-08-15 | 2018-03-07 | Axonics Modulation Technologies Inc. | Integrated electromyographic clinician programmer for use with an implantable neurostimulator |
| US9700731B2 (en) | 2014-08-15 | 2017-07-11 | Axonics Modulation Technologies, Inc. | Antenna and methods of use for an implantable nerve stimulator |
| CN107073258B (en) | 2014-08-15 | 2020-02-21 | 艾克索尼克斯调制技术股份有限公司 | System and method for neural stimulation electrode configuration based on neural localization |
| US10682521B2 (en) | 2014-08-15 | 2020-06-16 | Axonics Modulation Technologies, Inc. | Attachment devices and associated methods of use with a nerve stimulation charging device |
| JP6795491B2 (en) | 2014-08-15 | 2020-12-02 | アクソニクス モジュレーション テクノロジーズ インコーポレイテッド | Implantable lead attachment structure for nerve stimulation to relieve bladder dysfunction and other symptoms |
| US9884198B2 (en) | 2014-10-22 | 2018-02-06 | Nevro Corp. | Systems and methods for extending the life of an implanted pulse generator battery |
| CN107427675B (en) | 2015-01-09 | 2021-10-26 | 艾克索尼克斯股份有限公司 | Patient remote control and associated method for use with a neurostimulation system |
| AU2016205050B2 (en) | 2015-01-09 | 2020-02-27 | Axonics Modulation Technologies, Inc. | Attachment devices and associated methods of use with a nerve stimulation charging device |
| US9517344B1 (en) | 2015-03-13 | 2016-12-13 | Nevro Corporation | Systems and methods for selecting low-power, effective signal delivery parameters for an implanted pulse generator |
| US9943685B2 (en) | 2015-04-23 | 2018-04-17 | Cyberonics, Inc. | Lead engagement devices and methods for electrical stimulation and/or monitoring systems |
| JP6946261B2 (en) | 2015-07-10 | 2021-10-06 | アクソニクス インコーポレイテッド | Implantable nerve stimulators and methods with internal electronics without ASICs |
| US9517338B1 (en) | 2016-01-19 | 2016-12-13 | Axonics Modulation Technologies, Inc. | Multichannel clip device and methods of use |
| US10195423B2 (en) | 2016-01-19 | 2019-02-05 | Axonics Modulation Technologies, Inc. | Multichannel clip device and methods of use |
| JP6876363B2 (en) | 2016-01-29 | 2021-05-26 | アクソニクス モジュレーション テクノロジーズ インコーポレイテッド | Methods and systems for frequency adjustment that optimize the charging of implantable neurostimulators |
| US10376704B2 (en) | 2016-02-12 | 2019-08-13 | Axonics Modulation Technologies, Inc. | External pulse generator device and associated methods for trial nerve stimulation |
| JP2021513902A (en) | 2018-02-22 | 2021-06-03 | アクソニクス モジュレーション テクノロジーズ インコーポレイテッド | Nerve Stimulation Leads and Usage for Experimental Nerve Stimulation |
| US10933238B2 (en) | 2019-01-31 | 2021-03-02 | Nevro Corp. | Power control circuit for sterilized devices, and associated systems and methods |
| US11642537B2 (en) | 2019-03-11 | 2023-05-09 | Axonics, Inc. | Charging device with off-center coil |
| US11439829B2 (en) | 2019-05-24 | 2022-09-13 | Axonics, Inc. | Clinician programmer methods and systems for maintaining target operating temperatures |
| US11848090B2 (en) | 2019-05-24 | 2023-12-19 | Axonics, Inc. | Trainer for a neurostimulator programmer and associated methods of use with a neurostimulation system |
| USD1019950S1 (en) * | 2022-01-03 | 2024-03-26 | Axonics, Inc. | Header for an implantable medical device |
Family Cites Families (26)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4010760A (en) * | 1975-05-23 | 1977-03-08 | Medtronic, Inc. | Coupling assembly for implantable electromedical devices |
| US4010759A (en) * | 1975-08-29 | 1977-03-08 | Vitatron Medical B.V. | Insulated, corrosion resistant medical electronic devices and method for producing same |
| US4041956A (en) * | 1976-02-17 | 1977-08-16 | Coratomic, Inc. | Pacemakers of low weight and method of making such pacemakers |
| US4057068A (en) * | 1976-02-20 | 1977-11-08 | Medtronic, Inc. | Enclosure for and method of enclosing a body implantable pulse generator |
| ES479225A1 (en) | 1978-04-07 | 1979-12-01 | Medtronic Inc | Body implantable stimulator and connector therefor. |
| US4182345A (en) * | 1978-04-07 | 1980-01-08 | Medtronic, Inc. | Body implantable signal generator assembly |
| US4254775A (en) * | 1979-07-02 | 1981-03-10 | Mieczyslaw Mirowski | Implantable defibrillator and package therefor |
| US4262673A (en) * | 1979-10-11 | 1981-04-21 | Mieczyslaw Mirowski | Fluid tight coupling for electrode lead |
| FR2502502A1 (en) * | 1981-03-27 | 1982-10-01 | Cardiofrance Co | CARDIAC STIMULATOR COMPRISING A SINGLE ENCLOSURE FOR SEPARATING THE ELECTRIC CURRENT GENERATING AND IMPULSE GENERATING MEANS |
| US4764132A (en) * | 1986-03-28 | 1988-08-16 | Siemens-Pacesetter, Inc. | Pacemaker connector block for proximal ring electrode |
| US5070605A (en) * | 1988-04-22 | 1991-12-10 | Medtronic, Inc. | Method for making an in-line pacemaker connector system |
| US5235742A (en) * | 1989-11-20 | 1993-08-17 | Siemens Pacesetter, Inc. | Method of making an implantable device |
| US5076270A (en) * | 1990-05-03 | 1991-12-31 | Siemens-Pacesetter, Inc. | Apparatus and method for making electrical connections in an implantable pacemaker |
| US5086773A (en) * | 1990-09-10 | 1992-02-11 | Cardiac Pacemakers, Inc. | Tool-less pacemaker lead assembly |
| US5103818A (en) * | 1990-11-13 | 1992-04-14 | Siemens-Pacesetter, Inc. | System and method for completing electrical connections in an implantable medical device |
| US5336246A (en) * | 1993-06-23 | 1994-08-09 | Telectronics Pacing Systems, Inc. | Lead connector assembly for medical device and method of assembly |
| US5662692A (en) * | 1994-12-09 | 1997-09-02 | Pacesetter, Inc. | Cardiac defibrillator having selectable polarity case |
| US5549653A (en) * | 1995-09-22 | 1996-08-27 | Intermedics, Inc. | Muscle stimulation electrode for implantable cardial stimulation device with warning system |
| DE19622669A1 (en) * | 1996-06-05 | 1997-12-11 | Implex Gmbh | Implantable unit |
| US5643328A (en) * | 1996-07-19 | 1997-07-01 | Sulzer Intermedics Inc. | Implantable cardiac stimulation device with warning system having elongated stimulation electrode |
| US5741313A (en) * | 1996-09-09 | 1998-04-21 | Pacesetter, Inc. | Implantable medical device with a reduced volumetric configuration and improved shock stabilization |
| US5871514A (en) * | 1997-08-01 | 1999-02-16 | Medtronic, Inc. | Attachment apparatus for an implantable medical device employing ultrasonic energy |
| US5980973A (en) * | 1998-03-13 | 1999-11-09 | Medtronic, Inc. | Implantable medical device with biocompatible surface and method for its manufacture |
| US6026325A (en) * | 1998-06-18 | 2000-02-15 | Pacesetter, Inc. | Implantable medical device having an improved packaging system and method for making electrical connections |
| US6052623A (en) * | 1998-11-30 | 2000-04-18 | Medtronic, Inc. | Feedthrough assembly for implantable medical devices and methods for providing same |
| US6817905B2 (en) * | 2000-06-20 | 2004-11-16 | Medtronic, Inc. | Connector assembly for an implantable medical device and process for making |
-
2003
- 2003-11-05 CA CA002448376A patent/CA2448376A1/en not_active Abandoned
- 2003-11-05 EP EP03025398A patent/EP1417986A1/en not_active Withdrawn
- 2003-11-05 JP JP2003375467A patent/JP2004283550A/en active Pending
- 2003-11-05 US US10/701,849 patent/US7167749B2/en active Active
Also Published As
| Publication number | Publication date |
|---|---|
| US20040093038A1 (en) | 2004-05-13 |
| JP2004283550A (en) | 2004-10-14 |
| US7167749B2 (en) | 2007-01-23 |
| EP1417986A1 (en) | 2004-05-12 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US7167749B2 (en) | One piece header assembly for an implantable medical device | |
| US7069081B2 (en) | One piece header assembly for an implantable medical device | |
| US8706229B2 (en) | Connector assembly for connecting a lead and an implantable medical device | |
| JP4234606B2 (en) | Connector header for implantable medical device and manufacturing method thereof | |
| US8204596B2 (en) | Isolation connector for an intravascular implantable medical device | |
| US7322832B2 (en) | Radio frequency antenna flexible circuit interconnect with unique micro connectors | |
| JP4533380B2 (en) | Small size connector clip for implantable medical device | |
| EP1962948B1 (en) | Lead interconnections and reinforcement | |
| US20040034393A1 (en) | Connector port construction technique for implantable medical device | |
| US20050027326A1 (en) | Connector assembly for connecting a lead and an implantable medical device | |
| US20050043770A1 (en) | Multi-polar electrical medical lead connector system | |
| US20050043771A1 (en) | Multi-polar electrical medical lead connector system |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| EEER | Examination request | ||
| FZDE | Discontinued |