CA2216021C - High resolution brain stimulation lead and method of use - Google Patents
High resolution brain stimulation lead and method of use Download PDFInfo
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- CA2216021C CA2216021C CA002216021A CA2216021A CA2216021C CA 2216021 C CA2216021 C CA 2216021C CA 002216021 A CA002216021 A CA 002216021A CA 2216021 A CA2216021 A CA 2216021A CA 2216021 C CA2216021 C CA 2216021C
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- 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
- A61N1/0526—Head electrodes
- A61N1/0529—Electrodes for brain stimulation
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Abstract
A brain stimulation lead for precise delivery of electrical stimuli to a small dense brain target, and method of positioning such lead optimally in the patient's brain, is provided. The lead has a distal end portion which is substantially tubular or cylindrical along a longitudinal axis, and has a plurality of electrodes characterized by a diagonal geometry, permitting a greater number of electrodes to be provided within a very small lineal distance, e.g. 10 mm or even 5 mm. In a preferred embodiment, three ring electrodes are positioned on the distal end portion, each at a common angle of about 45 degrees and each extending only about 180 degrees around the lead body. The ring segment electrodes are about 0.5 mm in axial length, and have a separation of about 0.5 mm. The lead also has a tip electrode with a substantially spherical distal edge, and a proximal diagonal edge having the same angle as the ring segment electrodes. The diagonal ring geometry permits fine adjustment of the electrode assembly with respect to the target by simply rotating the lead about its axis, thereby facilitating an optimal electrode placement for precise stimulation of the target.
Description
' P-3434 PATENT
HIGH RESOLUTION BRAIN STIMULATION LEAD AND METHOD OF USE
FIELD OF THE INVENTION
This invention relates to brain stimulation leads and methods of employing such leads and, more particularly, a brain stimulation lead characterized by having a high resolution tip and method of placing such a lead.
BACKGROUND OF THE INVENTION
Brain stimulation leads designed to electrically stimulate nerve structures in specific areas of the brain are coming into increasing use. Deep brain stimulation has been used in the management of chronic intractable pain of neuropathic and or nociceptive origin.
In addition, brain stimulation is very important for treatment of movement disorders.
Implantation of a brain stimulation lead into a patient's brain, and delivery of stimulus pulses from a pulse generator to the lead electrodes, produces nerve impulses which may result in inhibition of pain. However, there is now a demand for such stimulation leads which are better able to stimulate exclusively certain selected small neurological targets, and without damage to involved brain tissue, which demand can not be met by existing leads. An example of such a small neurological brain target, for which extremely precise stimulation is needed, is the SubThalamic Nucleus (STN); another application is Globus Pallidus internal (Gpi) stimulation. Other like high density brain targets also require more precise stimulation than is 2 0 presently available.
The problem that is addressed requires a stimulation lead with high spatial resolution electrodes. The highest resolution lead presently available, such as the Model 3387 RESDBSTM, made by Medtronic, Inc., has plural electrodes, each with a length of 1.5 mm, and an electrode separation of 0.5 mm. For such a lead, only one of the four electrodes can be 2 5 positioned in a small target such as the STN. However, the functional spatial resolution in this target, combined with possible slight movements in the brain, require that more than one active electrode must be made available inside the target. Specifically, the need is to provide up to 4 electrodes within a 10 mm spacing, which imposes extreme requirements on lead construction. Additionally, it is desired to provide a brain stimulation lead, and method of using same, with a highly rigid, tip-bottomed stylet, to permit use of a stereotactic approach of the brain target, preferably without need for a guiding cannula.
SUN~iARY OF THE INVENTION
It is a primary object of this invention to provide a brain stimulation lead, and method of placing such lead, which presents an improved high spatial resolution tip carrying a plurality of electrodes that can be used in stimulating small neurological brain targets.
According to the invention there is provided a stimulation lead for delivery of electrical stimuli to a patient's brain, said lead having a longitudinal_ axis, a proximal end and a distal end portion, a first plurality of electrical conductors extending from said proximal end to said distal end, and a second plurality of electrodes positioned within said distal end portion, each said electrode being connected to a respective one of said conductors, each of said electrodes being a conductive ring;
characterized in that at least one conductive ring is diagonally positioned with respect to said longitudinal axis on said distal end portion.
In a preferred embodiment, the distal end is substantially cylindrical along a longitudinal axis, and each of the plurality of electrodes is diagonal7_y positioned at a common angle relative to the lead axis. Each ring electrode is diagonally around the lead axis anti may be separated from the adjacent electrodes by about 0.5 mm, 2a depending on the target. In addition, the lead may carry a distal tip electrode which is spherically configured at its distal end, and diagonally configured at its proximal end with the common angle to the axis. In a preferred embodiment, the lead distal portion carries three ring electrodes and a tip electrode, the four electrodes being positioned within a distance of no more than about 10 mm.
The ring electrodes may extend about 180 degrees around the lead axis, or may extend for a smaller or a greater angle.
In another embodiment, a greater number of ring segment electrodes are used, each electrode being less than 90 degrees around the lead, and the optimum plurality of electrodes is selected after testing different combinations of the ring segment electrodes at time of implant, or whenever an adjustment is desired.
In the method of this invention, the lead with high spatial resolution tip is positioned in the patient's brain with a stereotactic instrument, and adjusted axially, i.e., in an in-line direction. After this, finer tuning of the electrode positions for optimum stimulation is achieved simply by rotating the lead, thus re-arranging the relative positions of the ring segment electrodes within the target area.
BRIEF DESCRIPTION OF THE DRAWINGS
Figure lA is a diagrammatic drawing of the distal end of the brain stimulation lead of this invention, showing the relation of the electrodes to each other and to the main lead body, and illustrating the diagonal ring geometry.
Figure 1B is a cross section of the lead of Figure lA, taken along line A-A of Figure 1.
Figure 2 is a diagrammatic drawing of another embodiment of the brain stimulation lead of this invention, illustrating a distal portion having more than three ring segment diagonally spaced electrodes, the electrodes being positioned to provide a variety of electrode combination choices.
Figures 3A and 3B illustrate lead having diagonal ring electrodes characterized by a different surface geometry.
Figure 4 is a flow diagram illustrating the method of placing the high resolution lead of this invention.
DESCRIPTION OF THF P FFEILRFD EMBODIMENTS
Referring now to Figures lA and 1B, there is illustrated the preferred embodiment of the brain stimulation lead of this invention. The lead body 30 is tubular, or cylindrical in form, and has a proximal end (not shown) with suitable connectors for connecting to a pulse stimulator. Lead body 30 suitably has a coating of a biocompatible material such as polyurethane, with a diameter typically of about 0.13 cm.
Contained within the lead body is a mufti-conductor coil 32, each conductor being individually insulated, connecting the pulse generator to respective electrodes carried by the distal end portion of the 2 0 lead. The lead has a lumen, within coil 32, in which is placed a stylet shown as 34 at the time of implant. The use of a highly rigid stylet provides the possibility of performing stereotactic placement without the need of any addition aid such as a cannula. The use of a stereotactic instrument, and of a stylet, is well known in the art. See, for example, U.S.
Patent No.
5,464,446 .
Still referring to Figures lA and 1B, the design of the distal portion, which carries the ring segment electrodes, can be seen. In this exemplary embodiment, three ring segment electrodes are shown, at 40, 41 and 42. As seen in Figure 1B, each ring electrode illustrated as being about 180 degrees ; for this embodiment, each ring is a segment which preferably extends within a range of 180 degrees 145 . As used in describing this invention, 3 0 the term "ring" is not limited in terms of the angle that it extends around the lead axis, nor in terms of the exact geometry. See the illustration of Figures 4A and 4B, discussed hereinbelow. Each diagonal ring electrode is suitably made of platinum iridium and embedded into the biocompatible coating, and has an axial length D1 of about 0.4 to 0.5 mm, although it could be as great as 0.8 mm. The spacing D2 between each ring segment electrode is suitably about 0.5 mm, although it could be within a range of 0.5 to 1.5 mm, depending greatly on the application. The diagonal angle, as indicated, is ideally 45 degrees relative to the lead axis Ax, but can be plus/minus 15 degrees. The tip electrode 43 has a roughly spherical distal surface, an axial length of about 0.8 to 1.6 mm, and a distal boundary which is diagonal at the common angle of the ring electrodes, e.g., 45 degrees. The outer diameter D4 of the distal portion, which is positioned in the patient's brain, is preferably 0.5 mm, but can be in the range of 0.3 to 1.2 mm, depending on the application.
As seen in Figure 1B, for this embodiment, the ring segment is shown as 1 o extending about 180 degrees around the cylindrical distal body, although this angle can be adapted within a range of about 135 to 225 degrees. Each electrode is connected to a respective conductor Cl, C2, C3 or C4 by a laser weld, as illustrated at 40W, 41 W, 42W and 43 W.
Refernng now to Figure 2, there is shown an alternate embodiment characterized by more than three diagonal ring segment electrodes, each being less than 90 degrees in arc, and each being connected to a respective separate conductor, thereby providing a greater menu of effective electrode choices while maintaining the required high spatial resolution. In this example, there are six ring segment electrodes, designated 51-56, and a tip electrode 58, each of which has a common diagonal geometry to permit positioning of the 2 0 electrodes on the same size distal portion. In use of this lead, any two or more electrodes can be electrically connected together at the pulse generator site, to provide an optimal electrode configuration Referring now to Figures 3A and 3B, there is shown another illustration of a lead distal tip in accordance with this invention. In this embodiment, the electrodes 71, 72, 2 5 73, 74 are diagonally oriented, but have a curved surface geometry which contrasts with that of conventional ring electrodes. This illustrates that the invention is not limited in the exact form of the ring electrodes.
Referring now to Figure 4, there is shown a simplified flow diagram of the primary steps taken in carrying out the method of implanting and positioning the high 3 o resolution lead of this invention. It is assumed that the patient has been prepared in a standard fashion, e.g., a burr hole has been drilled and an anchoring system is ready.
At 60, the novel lead of this invention, and the appropriate stereotactic instrument are provided. At 61, the lead is inserted into the brain using the stereotactic instrument and the stylet. At 62, the lead is positioned axially, and tested at 63. If the axial placement is not satisfactory as determined at 64, steps 62 and 63 are repeated. When the distal portion of the lead is positioned at the desired depth with respect to the target in the brain, the lead is then rotated at 65, and the stimulation effectiveness is tested at 66. Rotation will provide, due to the diagonal geometry of the ring segment electrodes, a different stimulation profile, and fine tuning is thus provided which could not be obtained with conventional positioning of the lead. If the position is tested at 67 to not be OK, further rotation and testing is performed until the position is determined to be OK. Such testing can include trying different combinations of electrodes to find an optimum stimulation pattern. After this, the lead is anchored securely at 68, in a known manner.
There has thus been set forth an improved brain stimulation lead and method of placement, which provides a high spatial resolution as is required to optimally stimulate high density brain targets. Although a preferred and alternate embodiments have been set forth specifically, it is to be noted that other variations and equivalent embodiments which use the diagonal geometry of this invention are within the scope of the invention as claimed.
HIGH RESOLUTION BRAIN STIMULATION LEAD AND METHOD OF USE
FIELD OF THE INVENTION
This invention relates to brain stimulation leads and methods of employing such leads and, more particularly, a brain stimulation lead characterized by having a high resolution tip and method of placing such a lead.
BACKGROUND OF THE INVENTION
Brain stimulation leads designed to electrically stimulate nerve structures in specific areas of the brain are coming into increasing use. Deep brain stimulation has been used in the management of chronic intractable pain of neuropathic and or nociceptive origin.
In addition, brain stimulation is very important for treatment of movement disorders.
Implantation of a brain stimulation lead into a patient's brain, and delivery of stimulus pulses from a pulse generator to the lead electrodes, produces nerve impulses which may result in inhibition of pain. However, there is now a demand for such stimulation leads which are better able to stimulate exclusively certain selected small neurological targets, and without damage to involved brain tissue, which demand can not be met by existing leads. An example of such a small neurological brain target, for which extremely precise stimulation is needed, is the SubThalamic Nucleus (STN); another application is Globus Pallidus internal (Gpi) stimulation. Other like high density brain targets also require more precise stimulation than is 2 0 presently available.
The problem that is addressed requires a stimulation lead with high spatial resolution electrodes. The highest resolution lead presently available, such as the Model 3387 RESDBSTM, made by Medtronic, Inc., has plural electrodes, each with a length of 1.5 mm, and an electrode separation of 0.5 mm. For such a lead, only one of the four electrodes can be 2 5 positioned in a small target such as the STN. However, the functional spatial resolution in this target, combined with possible slight movements in the brain, require that more than one active electrode must be made available inside the target. Specifically, the need is to provide up to 4 electrodes within a 10 mm spacing, which imposes extreme requirements on lead construction. Additionally, it is desired to provide a brain stimulation lead, and method of using same, with a highly rigid, tip-bottomed stylet, to permit use of a stereotactic approach of the brain target, preferably without need for a guiding cannula.
SUN~iARY OF THE INVENTION
It is a primary object of this invention to provide a brain stimulation lead, and method of placing such lead, which presents an improved high spatial resolution tip carrying a plurality of electrodes that can be used in stimulating small neurological brain targets.
According to the invention there is provided a stimulation lead for delivery of electrical stimuli to a patient's brain, said lead having a longitudinal_ axis, a proximal end and a distal end portion, a first plurality of electrical conductors extending from said proximal end to said distal end, and a second plurality of electrodes positioned within said distal end portion, each said electrode being connected to a respective one of said conductors, each of said electrodes being a conductive ring;
characterized in that at least one conductive ring is diagonally positioned with respect to said longitudinal axis on said distal end portion.
In a preferred embodiment, the distal end is substantially cylindrical along a longitudinal axis, and each of the plurality of electrodes is diagonal7_y positioned at a common angle relative to the lead axis. Each ring electrode is diagonally around the lead axis anti may be separated from the adjacent electrodes by about 0.5 mm, 2a depending on the target. In addition, the lead may carry a distal tip electrode which is spherically configured at its distal end, and diagonally configured at its proximal end with the common angle to the axis. In a preferred embodiment, the lead distal portion carries three ring electrodes and a tip electrode, the four electrodes being positioned within a distance of no more than about 10 mm.
The ring electrodes may extend about 180 degrees around the lead axis, or may extend for a smaller or a greater angle.
In another embodiment, a greater number of ring segment electrodes are used, each electrode being less than 90 degrees around the lead, and the optimum plurality of electrodes is selected after testing different combinations of the ring segment electrodes at time of implant, or whenever an adjustment is desired.
In the method of this invention, the lead with high spatial resolution tip is positioned in the patient's brain with a stereotactic instrument, and adjusted axially, i.e., in an in-line direction. After this, finer tuning of the electrode positions for optimum stimulation is achieved simply by rotating the lead, thus re-arranging the relative positions of the ring segment electrodes within the target area.
BRIEF DESCRIPTION OF THE DRAWINGS
Figure lA is a diagrammatic drawing of the distal end of the brain stimulation lead of this invention, showing the relation of the electrodes to each other and to the main lead body, and illustrating the diagonal ring geometry.
Figure 1B is a cross section of the lead of Figure lA, taken along line A-A of Figure 1.
Figure 2 is a diagrammatic drawing of another embodiment of the brain stimulation lead of this invention, illustrating a distal portion having more than three ring segment diagonally spaced electrodes, the electrodes being positioned to provide a variety of electrode combination choices.
Figures 3A and 3B illustrate lead having diagonal ring electrodes characterized by a different surface geometry.
Figure 4 is a flow diagram illustrating the method of placing the high resolution lead of this invention.
DESCRIPTION OF THF P FFEILRFD EMBODIMENTS
Referring now to Figures lA and 1B, there is illustrated the preferred embodiment of the brain stimulation lead of this invention. The lead body 30 is tubular, or cylindrical in form, and has a proximal end (not shown) with suitable connectors for connecting to a pulse stimulator. Lead body 30 suitably has a coating of a biocompatible material such as polyurethane, with a diameter typically of about 0.13 cm.
Contained within the lead body is a mufti-conductor coil 32, each conductor being individually insulated, connecting the pulse generator to respective electrodes carried by the distal end portion of the 2 0 lead. The lead has a lumen, within coil 32, in which is placed a stylet shown as 34 at the time of implant. The use of a highly rigid stylet provides the possibility of performing stereotactic placement without the need of any addition aid such as a cannula. The use of a stereotactic instrument, and of a stylet, is well known in the art. See, for example, U.S.
Patent No.
5,464,446 .
Still referring to Figures lA and 1B, the design of the distal portion, which carries the ring segment electrodes, can be seen. In this exemplary embodiment, three ring segment electrodes are shown, at 40, 41 and 42. As seen in Figure 1B, each ring electrode illustrated as being about 180 degrees ; for this embodiment, each ring is a segment which preferably extends within a range of 180 degrees 145 . As used in describing this invention, 3 0 the term "ring" is not limited in terms of the angle that it extends around the lead axis, nor in terms of the exact geometry. See the illustration of Figures 4A and 4B, discussed hereinbelow. Each diagonal ring electrode is suitably made of platinum iridium and embedded into the biocompatible coating, and has an axial length D1 of about 0.4 to 0.5 mm, although it could be as great as 0.8 mm. The spacing D2 between each ring segment electrode is suitably about 0.5 mm, although it could be within a range of 0.5 to 1.5 mm, depending greatly on the application. The diagonal angle, as indicated, is ideally 45 degrees relative to the lead axis Ax, but can be plus/minus 15 degrees. The tip electrode 43 has a roughly spherical distal surface, an axial length of about 0.8 to 1.6 mm, and a distal boundary which is diagonal at the common angle of the ring electrodes, e.g., 45 degrees. The outer diameter D4 of the distal portion, which is positioned in the patient's brain, is preferably 0.5 mm, but can be in the range of 0.3 to 1.2 mm, depending on the application.
As seen in Figure 1B, for this embodiment, the ring segment is shown as 1 o extending about 180 degrees around the cylindrical distal body, although this angle can be adapted within a range of about 135 to 225 degrees. Each electrode is connected to a respective conductor Cl, C2, C3 or C4 by a laser weld, as illustrated at 40W, 41 W, 42W and 43 W.
Refernng now to Figure 2, there is shown an alternate embodiment characterized by more than three diagonal ring segment electrodes, each being less than 90 degrees in arc, and each being connected to a respective separate conductor, thereby providing a greater menu of effective electrode choices while maintaining the required high spatial resolution. In this example, there are six ring segment electrodes, designated 51-56, and a tip electrode 58, each of which has a common diagonal geometry to permit positioning of the 2 0 electrodes on the same size distal portion. In use of this lead, any two or more electrodes can be electrically connected together at the pulse generator site, to provide an optimal electrode configuration Referring now to Figures 3A and 3B, there is shown another illustration of a lead distal tip in accordance with this invention. In this embodiment, the electrodes 71, 72, 2 5 73, 74 are diagonally oriented, but have a curved surface geometry which contrasts with that of conventional ring electrodes. This illustrates that the invention is not limited in the exact form of the ring electrodes.
Referring now to Figure 4, there is shown a simplified flow diagram of the primary steps taken in carrying out the method of implanting and positioning the high 3 o resolution lead of this invention. It is assumed that the patient has been prepared in a standard fashion, e.g., a burr hole has been drilled and an anchoring system is ready.
At 60, the novel lead of this invention, and the appropriate stereotactic instrument are provided. At 61, the lead is inserted into the brain using the stereotactic instrument and the stylet. At 62, the lead is positioned axially, and tested at 63. If the axial placement is not satisfactory as determined at 64, steps 62 and 63 are repeated. When the distal portion of the lead is positioned at the desired depth with respect to the target in the brain, the lead is then rotated at 65, and the stimulation effectiveness is tested at 66. Rotation will provide, due to the diagonal geometry of the ring segment electrodes, a different stimulation profile, and fine tuning is thus provided which could not be obtained with conventional positioning of the lead. If the position is tested at 67 to not be OK, further rotation and testing is performed until the position is determined to be OK. Such testing can include trying different combinations of electrodes to find an optimum stimulation pattern. After this, the lead is anchored securely at 68, in a known manner.
There has thus been set forth an improved brain stimulation lead and method of placement, which provides a high spatial resolution as is required to optimally stimulate high density brain targets. Although a preferred and alternate embodiments have been set forth specifically, it is to be noted that other variations and equivalent embodiments which use the diagonal geometry of this invention are within the scope of the invention as claimed.
Claims (20)
1. A stimulation lead for delivery of electrical stimuli to a patient's brain, said lead having a longitudinal axis, a proximal end and a distal end portion, a first plurality of electrical conductors extending from said proximal end to said distal end, and a second plurality of electrodes positioned within said distal end portion, each said electrode being connected to a respective one of said conductors, each of said electrodes being a conductive ring;
characterized in that at least one conductive ring is diagonally positioned with respect to said longitudinal axis on said distal end portion.
characterized in that at least one conductive ring is diagonally positioned with respect to said longitudinal axis on said distal end portion.
2. The lead as described in claim 1, wherein each of said conductive ring electrodes is diagonally positioned at a common angle with respect to said axis, said angle being 45 ~ 15 degrees.
3. The lead as described in claim 2, further comprising a tip electrode at the distal tip end of said distal end portion, said tip electrode being connected to one of said conductors.
4. The lead as described in claim 3, wherein said first plurality of conductors comprises 4 conductors, and said second plurality of electrodes comprises 3 ring electrodes.
5. The lead as described in claim 3, wherein said distal end portion has a length of no more than 5 mm.
6. The lead as described in claim 3, wherein there is a separation of about 0.4 to 0.8 mm between each of said electrodes.
7. The lead as described in claim 3, wherein said tip electrode has a diagonal proximal edge at said common angle.
8. The lead as described in claim 3, wherein each of said ring electrodes has a longitudinal width of no more than 0.5 mm.
9. The lead as described in claim 3, wherein said biocompatible coating is polyurethane, and said electrodes are embedded in said material.
10. The lead as described in claim 3, wherein said distal portion has an outer diameter no greater than 0.5 mm.
11. The lead as described in claim 1, wherein said ring electrodes extend around said distal end portion an angular distance in a range of 135-180 degrees.
12. The lead as described in claim 1, wherein said distal end portion is injection molded.
13. The lead as described in claim 3, wherein said tip electrode is spherically configured at its distal end, and diagonally configured at its proximal end.
14. The lead as described in claim 1, wherein each said ring electrode extends around said axis by an angle within the range of 135-225 degrees.
15. The lead as described in claim 1, wherein said distal end portion being cylindrical along a longitudinal axis.
16. The lead as described in claim 1 wherein said distal end portion has a length of less than 10 mm.
17. The lead as described in claim 1 further comprising a biocompatible outer coating.
18. A stimulation lead for delivery of electrical stimuli to a patient's brain, said lead having a longitudinal axis, a proximal end and a distal end portion, said distal end portion being no greater than 5 mm, said distal end portion having a plurality of conductive ring electrodes positioned at a common diagonal angle with respect to the longitudinal axis of said lead, and a plurality of electrical conductors connecting from respective ones of said electrodes to said lead proximal end.
19. The lead as described in claim 18, wherein each of said ring electrodes extends around said lead by an angle which is less than 180 degrees.
20. The lead as described in claim 18, wherein each of said ring electrodes extends around said lead by an angle which is at least 180 degrees.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US08/721,816 US5843148A (en) | 1996-09-27 | 1996-09-27 | High resolution brain stimulation lead and method of use |
| US08/721,816 | 1996-09-27 |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2216021A1 CA2216021A1 (en) | 1998-03-27 |
| CA2216021C true CA2216021C (en) | 2005-09-13 |
Family
ID=24899419
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002216021A Expired - Fee Related CA2216021C (en) | 1996-09-27 | 1997-09-22 | High resolution brain stimulation lead and method of use |
Country Status (6)
| Country | Link |
|---|---|
| US (1) | US5843148A (en) |
| EP (1) | EP0832667B1 (en) |
| JP (1) | JPH10137346A (en) |
| AU (1) | AU726391B2 (en) |
| CA (1) | CA2216021C (en) |
| DE (1) | DE69727749T2 (en) |
Families Citing this family (211)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6330466B1 (en) * | 1998-02-23 | 2001-12-11 | California Institute Of Technology | Using a multi-electrode probe in creating an electrophysiological profile during stereotactic neurosurgery |
| US6238340B1 (en) * | 1998-05-19 | 2001-05-29 | Eckhard Alt | Composite materials for avoidance of unwanted radiation amplification |
| US6216045B1 (en) * | 1999-04-26 | 2001-04-10 | Advanced Neuromodulation Systems, Inc. | Implantable lead and method of manufacture |
| US6539263B1 (en) * | 1999-06-11 | 2003-03-25 | Cornell Research Foundation, Inc. | Feedback mechanism for deep brain stimulation |
| US6343226B1 (en) * | 1999-06-25 | 2002-01-29 | Neurokinetic Aps | Multifunction electrode for neural tissue stimulation |
| DE10044115A1 (en) | 1999-09-13 | 2001-04-12 | Medtronic Inc | Combined micro-macro-brain stimulation lead and method of use |
| US6587733B1 (en) * | 2000-02-08 | 2003-07-01 | Medtronic, Inc. | Percutaneous surgical lead body with directed stimulation |
| US20090209831A1 (en) * | 2000-06-28 | 2009-08-20 | Nexgen Medical Systems, Incorporated | Imaging methods for visualizing implanted living cells |
| US7305268B2 (en) | 2000-07-13 | 2007-12-04 | Northstar Neurscience, Inc. | Systems and methods for automatically optimizing stimulus parameters and electrode configurations for neuro-stimulators |
| US7831305B2 (en) | 2001-10-15 | 2010-11-09 | Advanced Neuromodulation Systems, Inc. | Neural stimulation system and method responsive to collateral neural activity |
| US7024247B2 (en) | 2001-10-15 | 2006-04-04 | Northstar Neuroscience, Inc. | Systems and methods for reducing the likelihood of inducing collateral neural activity during neural stimulation threshold test procedures |
| US7010351B2 (en) | 2000-07-13 | 2006-03-07 | Northstar Neuroscience, Inc. | Methods and apparatus for effectuating a lasting change in a neural-function of a patient |
| US7236831B2 (en) * | 2000-07-13 | 2007-06-26 | Northstar Neuroscience, Inc. | Methods and apparatus for effectuating a lasting change in a neural-function of a patient |
| US7756584B2 (en) | 2000-07-13 | 2010-07-13 | Advanced Neuromodulation Systems, Inc. | Methods and apparatus for effectuating a lasting change in a neural-function of a patient |
| US7146217B2 (en) | 2000-07-13 | 2006-12-05 | Northstar Neuroscience, Inc. | Methods and apparatus for effectuating a change in a neural-function of a patient |
| US7672730B2 (en) | 2001-03-08 | 2010-03-02 | Advanced Neuromodulation Systems, Inc. | Methods and apparatus for effectuating a lasting change in a neural-function of a patient |
| US6529774B1 (en) | 2000-11-09 | 2003-03-04 | Neuropace, Inc. | Extradural leads, neurostimulator assemblies, and processes of using them for somatosensory and brain stimulation |
| US7212867B2 (en) * | 2000-12-07 | 2007-05-01 | Medtronic, Inc. | Directional brain stimulation and recording leads |
| US7033326B1 (en) | 2000-12-29 | 2006-04-25 | Advanced Bionics Corporation | Systems and methods of implanting a lead for brain stimulation |
| US7177701B1 (en) | 2000-12-29 | 2007-02-13 | Advanced Bionics Corporation | System for permanent electrode placement utilizing microelectrode recording methods |
| GB0104982D0 (en) * | 2001-02-28 | 2001-04-18 | Gill Steven | Electrode |
| US7299096B2 (en) | 2001-03-08 | 2007-11-20 | Northstar Neuroscience, Inc. | System and method for treating Parkinson's Disease and other movement disorders |
| US6560472B2 (en) | 2001-06-21 | 2003-05-06 | Microhelix, Inc. | Multi-channel structurally robust brain probe and method of making the same |
| US20090069706A1 (en) * | 2001-06-21 | 2009-03-12 | Jerome Boogaard | Brain probe adapted to be introduced through a canula |
| US6606521B2 (en) | 2001-07-09 | 2003-08-12 | Neuropace, Inc. | Implantable medical lead |
| US6662035B2 (en) | 2001-09-13 | 2003-12-09 | Neuropace, Inc. | Implantable lead connector assembly for implantable devices and methods of using it |
| AUPR851601A0 (en) * | 2001-10-26 | 2001-11-29 | Cochlear Limited | Auditory midbrain implant |
| US6758828B2 (en) | 2001-12-10 | 2004-07-06 | Regents Of The University Of Minnesota | Catheter for cell delivery in tissue |
| US7221981B2 (en) | 2002-03-28 | 2007-05-22 | Northstar Neuroscience, Inc. | Electrode geometries for efficient neural stimulation |
| US7860570B2 (en) | 2002-06-20 | 2010-12-28 | Boston Scientific Neuromodulation Corporation | Implantable microstimulators and methods for unidirectional propagation of action potentials |
| US20040049121A1 (en) * | 2002-09-06 | 2004-03-11 | Uri Yaron | Positioning system for neurological procedures in the brain |
| US7082335B2 (en) * | 2002-09-30 | 2006-07-25 | Medtronic, Inc. | Multipolar pacing method and apparatus |
| US7797057B2 (en) * | 2002-10-23 | 2010-09-14 | Medtronic, Inc. | Medical paddle lead and method for spinal cord stimulation |
| US7236830B2 (en) | 2002-12-10 | 2007-06-26 | Northstar Neuroscience, Inc. | Systems and methods for enhancing or optimizing neural stimulation therapy for treating symptoms of Parkinson's disease and/or other movement disorders |
| US7035690B2 (en) | 2002-11-15 | 2006-04-25 | Medtronic, Inc. | Human-implantable-neurostimulator user interface having multiple levels of abstraction |
| US20050075680A1 (en) | 2003-04-18 | 2005-04-07 | Lowry David Warren | Methods and systems for intracranial neurostimulation and/or sensing |
| US7302298B2 (en) | 2002-11-27 | 2007-11-27 | Northstar Neuroscience, Inc | Methods and systems employing intracranial electrodes for neurostimulation and/or electroencephalography |
| US6959215B2 (en) | 2002-12-09 | 2005-10-25 | Northstar Neuroscience, Inc. | Methods for treating essential tremor |
| CA2508800A1 (en) * | 2002-12-11 | 2004-06-24 | Proteus Biomedical, Inc. | Method and system for monitoring and treating hemodynamic parameters |
| AU2004251021A1 (en) | 2003-04-24 | 2005-01-06 | Advanced Neuromodulation Systems, Inc. | Systems and methods for facilitating and/or effectuating development, rehabilitation, restoration, and/or recovery of visual function through neural stimulation |
| JP2007501067A (en) | 2003-08-01 | 2007-01-25 | ノーススター ニューロサイエンス インコーポレイテッド | Apparatus and method for applying neural stimulation to patient |
| EP1680180B1 (en) * | 2003-10-02 | 2007-02-28 | Medtronic, Inc. | Implantable medical lead and method of manufacture |
| GB0413076D0 (en) | 2004-06-11 | 2004-07-14 | Medtronic Inc | Deep brain stimulation of the Zona incerta |
| US7346382B2 (en) | 2004-07-07 | 2008-03-18 | The Cleveland Clinic Foundation | Brain stimulation models, systems, devices, and methods |
| JP2008506464A (en) | 2004-07-15 | 2008-03-06 | ノーススター ニューロサイエンス インコーポレイテッド | System and method for enhancing or influencing neural stimulation efficiency and / or efficacy |
| WO2006015087A2 (en) * | 2004-07-27 | 2006-02-09 | The Cleveland Clinic Foundation | Thalamic stimulation device |
| DE102004037739A1 (en) | 2004-08-04 | 2006-03-16 | Degussa Ag | Tungstate-containing catalysts for the synthesis of alkylmercaptan and process for their preparation |
| US20060041284A1 (en) * | 2004-08-17 | 2006-02-23 | Advanced Neuromodulation Systems, Inc. | Electrical stimulation system and method for stimulating nerve tissue in the brain using a stimulation lead having a tip electrode, having at least five electrodes, or both |
| US20060161216A1 (en) * | 2004-10-18 | 2006-07-20 | John Constance M | Device for neuromuscular peripheral body stimulation and electrical stimulation (ES) for wound healing using RF energy harvesting |
| US7565200B2 (en) | 2004-11-12 | 2009-07-21 | Advanced Neuromodulation Systems, Inc. | Systems and methods for selecting stimulation sites and applying treatment, including treatment of symptoms of Parkinson's disease, other movement disorders, and/or drug side effects |
| US7783359B2 (en) * | 2005-01-05 | 2010-08-24 | Boston Scientific Neuromodulation Corporation | Devices and methods using an implantable pulse generator for brain stimulation |
| US7809446B2 (en) * | 2005-01-05 | 2010-10-05 | Boston Scientific Neuromodulation Corporation | Devices and methods for brain stimulation |
| US7761985B2 (en) * | 2005-01-31 | 2010-07-27 | Medtronic, Inc. | Method of manufacturing a medical lead |
| JP4742356B2 (en) * | 2005-02-02 | 2011-08-10 | 独立行政法人産業技術総合研究所 | Embedded electrode device and electrode embedded device |
| US8644941B2 (en) | 2005-06-09 | 2014-02-04 | Medtronic, Inc. | Peripheral nerve field stimulation and spinal cord stimulation |
| DE602006019869D1 (en) * | 2005-06-09 | 2011-03-10 | Medtronic Inc | IMPLANTABLE MEDICAL MANAGEMENT |
| US8620435B2 (en) | 2005-06-09 | 2013-12-31 | Medtronic, Inc. | Combination therapy including peripheral nerve field stimulation |
| US8271094B1 (en) * | 2005-09-30 | 2012-09-18 | Boston Scientific Neuromodulation Corporation | Devices with cannula and electrode lead for brain stimulation and methods of use and manufacture |
| US7856264B2 (en) | 2005-10-19 | 2010-12-21 | Advanced Neuromodulation Systems, Inc. | Systems and methods for patient interactive neural stimulation and/or chemical substance delivery |
| US7729773B2 (en) | 2005-10-19 | 2010-06-01 | Advanced Neuromodualation Systems, Inc. | Neural stimulation and optical monitoring systems and methods |
| US8929991B2 (en) | 2005-10-19 | 2015-01-06 | Advanced Neuromodulation Systems, Inc. | Methods for establishing parameters for neural stimulation, including via performance of working memory tasks, and associated kits |
| DE102006008501B3 (en) * | 2006-02-23 | 2007-10-25 | Albert-Ludwigs-Universität Freiburg | Probe and method for data transfer between a brain and a data processing device |
| US8612024B2 (en) | 2006-02-24 | 2013-12-17 | Medtronic, Inc. | User interface with 3D environment for configuring stimulation therapy |
| US8380321B2 (en) | 2006-02-24 | 2013-02-19 | Medtronic, Inc. | Programming interface with a cross-sectional view of a stimulation lead with complex electrode array geometry |
| US20070203538A1 (en) | 2006-02-24 | 2007-08-30 | Medtronic, Inc. | User interface with an atlas for configuring stimulation therapy |
| US8321025B2 (en) * | 2006-07-31 | 2012-11-27 | Cranial Medical Systems, Inc. | Lead and methods for brain monitoring and modulation |
| US7583999B2 (en) | 2006-07-31 | 2009-09-01 | Cranial Medical Systems, Inc. | Multi-channel connector for brain stimulation system |
| WO2008038208A2 (en) | 2006-09-26 | 2008-04-03 | Koninklijke Philips Electronics, N.V. | Tissue stimulation method and apparatus |
| US20080154331A1 (en) * | 2006-12-21 | 2008-06-26 | Varghese John | Device for multicentric brain modulation, repair and interface |
| US7987001B2 (en) | 2007-01-25 | 2011-07-26 | Warsaw Orthopedic, Inc. | Surgical navigational and neuromonitoring instrument |
| US8374673B2 (en) | 2007-01-25 | 2013-02-12 | Warsaw Orthopedic, Inc. | Integrated surgical navigational and neuromonitoring system having automated surgical assistance and control |
| US20100100152A1 (en) * | 2007-03-02 | 2010-04-22 | Koninklijke Philips Electronics N.V. | Electrode system for deep brain stimulation |
| US9561053B2 (en) | 2007-04-25 | 2017-02-07 | Medtronic, Inc. | Implant tool to facilitate medical device implantation |
| US9399130B2 (en) | 2007-04-25 | 2016-07-26 | Medtronic, Inc. | Cannula configured to deliver test stimulation |
| WO2008133616A1 (en) * | 2007-04-26 | 2008-11-06 | Medtronic, Inc. | Implantable medical lead with multiple electrode configurations |
| US7668601B2 (en) * | 2007-04-26 | 2010-02-23 | Medtronic, Inc. | Implantable medical lead with multiple electrode configurations |
| WO2008144232A2 (en) | 2007-05-18 | 2008-11-27 | The Johns Hopkins University | A treatment simulator for brain diseases and method of use thereof |
| US9592377B2 (en) * | 2007-07-27 | 2017-03-14 | Second Sight Medical Products, Inc. | Implantable device for the brain |
| US8295943B2 (en) | 2007-08-20 | 2012-10-23 | Medtronic, Inc. | Implantable medical lead with biased electrode |
| WO2009025817A2 (en) | 2007-08-20 | 2009-02-26 | Medtronic, Inc. | Evaluating therapeutic stimulation electrode configurations based on physiological responses |
| US20090054947A1 (en) * | 2007-08-20 | 2009-02-26 | Medtronic, Inc. | Electrode configurations for directional leads |
| WO2009052425A1 (en) | 2007-10-17 | 2009-04-23 | Neuronexus Technologies | Implantable device including a resorbable carrier |
| US9220889B2 (en) | 2008-02-11 | 2015-12-29 | Intelect Medical, Inc. | Directional electrode devices with locating features |
| US8019440B2 (en) | 2008-02-12 | 2011-09-13 | Intelect Medical, Inc. | Directional lead assembly |
| US9272153B2 (en) | 2008-05-15 | 2016-03-01 | Boston Scientific Neuromodulation Corporation | VOA generation system and method using a fiber specific analysis |
| US8788042B2 (en) | 2008-07-30 | 2014-07-22 | Ecole Polytechnique Federale De Lausanne (Epfl) | Apparatus and method for optimized stimulation of a neurological target |
| US8359107B2 (en) * | 2008-10-09 | 2013-01-22 | Boston Scientific Neuromodulation Corporation | Electrode design for leads of implantable electric stimulation systems and methods of making and using |
| US8788064B2 (en) | 2008-11-12 | 2014-07-22 | Ecole Polytechnique Federale De Lausanne | Microfabricated neurostimulation device |
| KR101129364B1 (en) | 2008-12-10 | 2012-03-26 | 한국전자통신연구원 | An electrode for cerebral nerve stimulus and a substrate comprising the electrode |
| US20140255461A9 (en) * | 2009-02-10 | 2014-09-11 | Richard Jay McMurtrey | Decorin and Gliosis and Related System and Method |
| DE102009015723B4 (en) * | 2009-03-31 | 2013-12-19 | Forschungszentrum Jülich GmbH | stimulation electrode |
| AU2010236196B2 (en) | 2009-04-16 | 2015-11-12 | Boston Scientific Neuromodulation Corporation | Deep brain stimulation current steering with split electrodes |
| US8694123B2 (en) * | 2009-06-19 | 2014-04-08 | Medtronic, Inc. | Helical electrode arrangements for medical leads |
| WO2010148377A1 (en) | 2009-06-19 | 2010-12-23 | Medtronic, Inc. | Electrode arrangements for suborbital foramen medical lead |
| US8509920B2 (en) | 2009-06-19 | 2013-08-13 | Medtronic, Inc. | Electrode arrangements for medical lead |
| WO2011000791A1 (en) | 2009-06-29 | 2011-01-06 | 3Win N.V. | Atraumatic lead for deep brain stimulation |
| US8875391B2 (en) | 2009-07-07 | 2014-11-04 | Boston Scientific Neuromodulation Corporation | Methods for making leads with radially-aligned segmented electrodes for electrical stimulation systems |
| US8887387B2 (en) | 2009-07-07 | 2014-11-18 | Boston Scientific Neuromodulation Corporation | Methods of manufacture of leads with a radially segmented electrode array |
| US8543222B1 (en) | 2009-08-14 | 2013-09-24 | Jerzy Roman Sochor | Implantable lead and accessories |
| JP5734295B2 (en) | 2009-08-27 | 2015-06-17 | ザ クリーブランド クリニック ファウンデーション | System and method for estimating a site of tissue activity |
| EP2493564B1 (en) | 2009-10-29 | 2016-07-13 | Aortech International plc | Polyurethane header formed directly on implantable electrical devices |
| US8391985B2 (en) | 2009-11-30 | 2013-03-05 | Boston Scientific Neuromodulation Corporation | Electrode array having concentric windowed cylinder electrodes and methods of making the same |
| US8295944B2 (en) | 2009-11-30 | 2012-10-23 | Boston Scientific Neuromodulation Corporation | Electrode array with electrodes having cutout portions and methods of making the same |
| US8874232B2 (en) * | 2009-11-30 | 2014-10-28 | Boston Scientific Neuromodulation Corporation | Electrode array having concentric split ring electrodes and methods of making the same |
| US8788063B2 (en) | 2009-11-30 | 2014-07-22 | Boston Scientific Neuromodulation Corporation | Electrode array having a rail system and methods of manufacturing the same |
| EP2506920B1 (en) | 2009-12-01 | 2016-07-13 | Ecole Polytechnique Fédérale de Lausanne | Microfabricated surface neurostimulation device and method of making the same |
| WO2011068997A1 (en) | 2009-12-02 | 2011-06-09 | The Cleveland Clinic Foundation | Reversing cognitive-motor impairments in patients having a neuro-degenerative disease using a computational modeling approach to deep brain stimulation programming |
| KR101156081B1 (en) * | 2010-03-10 | 2012-06-20 | 주식회사 엠아이텍 | Apparatus for making a multi-channel electrode in an Intracranial Stimulating and Method thereof |
| CA2792153C (en) * | 2010-03-23 | 2018-05-15 | Boston Scientific Neuromodulation Corporation | Helical radial spacing of contacts on a cylindrical lead |
| WO2011121089A1 (en) | 2010-04-01 | 2011-10-06 | Ecole Polytechnique Federale De Lausanne (Epfl) | Device for interacting with neurological tissue and methods of making and using the same |
| US8968331B1 (en) | 2010-04-24 | 2015-03-03 | Jerzy Roman Sochor | Implantable lead and surgical accessories |
| JP5830090B2 (en) | 2010-06-14 | 2015-12-09 | ボストン サイエンティフィック ニューロモデュレイション コーポレイション | Programming interface for spinal nerve regulation |
| US8868206B2 (en) | 2010-06-18 | 2014-10-21 | Boston Scientific Neuromodulation Corporation | Electrode array having embedded electrodes and methods of making the same |
| JP5940532B2 (en) | 2010-07-16 | 2016-06-29 | ボストン サイエンティフィック ニューロモデュレイション コーポレイション | System for radial steering of electrode arrays |
| US8583237B2 (en) | 2010-09-13 | 2013-11-12 | Cranial Medical Systems, Inc. | Devices and methods for tissue modulation and monitoring |
| JP5808813B2 (en) | 2010-09-21 | 2015-11-10 | ボストン サイエンティフィック ニューロモデュレイション コーポレイション | Electrical stimulation lead and method for forming a lead for a stimulation device |
| US8965482B2 (en) | 2010-09-30 | 2015-02-24 | Nevro Corporation | Systems and methods for positioning implanted devices in a patient |
| US8805519B2 (en) | 2010-09-30 | 2014-08-12 | Nevro Corporation | Systems and methods for detecting intrathecal penetration |
| EP2881139B1 (en) | 2010-12-23 | 2021-10-06 | Boston Scientific Neuromodulation Corporation | Method and assembly for making a medical lead including removing connectors by grinding |
| WO2012095529A1 (en) * | 2011-01-14 | 2012-07-19 | Sapiens Steering Brain Stimulation B.V. | Brain mapping probe |
| US8700179B2 (en) | 2011-02-02 | 2014-04-15 | Boston Scientific Neuromodulation Corporation | Leads with spiral of helical segmented electrode arrays and methods of making and using the leads |
| EP2673043B1 (en) | 2011-02-08 | 2015-08-19 | Boston Scientific Neuromodulation Corporation | Leads with segmented electrodes for electrical stimulation systems |
| ES2801326T3 (en) | 2011-02-08 | 2021-01-11 | Boston Scient Neuromodulation Corp | Spirally arranged lead wires with segmented electrodes and lead wire manufacturing and use procedures |
| US20120203316A1 (en) | 2011-02-08 | 2012-08-09 | Boston Scientific Neuromodulation Corporation | Leads with segmented electrodes for electrical stimulation of planar regions and methods of making and using |
| US8818525B2 (en) * | 2011-02-11 | 2014-08-26 | Medtronic, Inc. | Lead having thin distal end portion |
| JP2014513622A (en) | 2011-03-29 | 2014-06-05 | ボストン サイエンティフィック ニューロモデュレイション コーポレイション | Communication interface for therapeutic stimulus delivery system |
| US9592389B2 (en) | 2011-05-27 | 2017-03-14 | Boston Scientific Neuromodulation Corporation | Visualization of relevant stimulation leadwire electrodes relative to selected stimulation information |
| AU2012294364A1 (en) | 2011-08-09 | 2014-03-20 | Boston Scientific Neuromodulation Corporation | Remote control for blind clinical trials of electrical stimulation |
| EP2790773B1 (en) | 2012-01-25 | 2020-10-14 | Nevro Corporation | Lead anchor |
| WO2013112905A1 (en) | 2012-01-26 | 2013-08-01 | Boston Scientific Neuromodulation Corporation | Systems and methods for identifying the circumferential positioning of electrodes of leads for electrical stimulation systems |
| US8744596B2 (en) | 2012-03-30 | 2014-06-03 | Boston Scientific Neuromodulation Corporation | Leads with X-ray fluorescent capsules for electrode identification and methods of manufacture and use |
| EP2841149B1 (en) | 2012-04-27 | 2020-07-08 | Medtronic, Inc. | Method and system for fabricating a medical lead using an electrode fixture |
| EP2854936B1 (en) | 2012-06-01 | 2016-05-25 | Boston Scientific Neuromodulation Corporation | Leads with tip electrode for electrical stimulation systems and methods of making and using |
| US8897891B2 (en) | 2012-08-03 | 2014-11-25 | Boston Scientific Neuromodulation Corporation | Leads with electrode carrier for segmented electrodes and methods of making and using |
| EP2879757B1 (en) | 2012-08-04 | 2019-06-26 | Boston Scientific Neuromodulation Corporation | Systems and methods for storing and transferring registration, atlas, and lead information between medical devices |
| EP2891091B1 (en) | 2012-08-28 | 2018-01-31 | Boston Scientific Neuromodulation Corporation | Capture and visualization of clinical effects data in relation to a lead and/or locus of stimulation |
| US9295838B2 (en) | 2012-10-31 | 2016-03-29 | The Regents Of The University Of California | Methods and systems for treating neurological movement disorders |
| US9792412B2 (en) | 2012-11-01 | 2017-10-17 | Boston Scientific Neuromodulation Corporation | Systems and methods for VOA model generation and use |
| US9308022B2 (en) | 2012-12-10 | 2016-04-12 | Nevro Corporation | Lead insertion devices and associated systems and methods |
| CN105246543A (en) | 2013-05-15 | 2016-01-13 | 波士顿科学神经调制公司 | Systems and methods for making tip electrodes for leads of electrical stimulation systems |
| CA2911239A1 (en) | 2013-05-31 | 2014-12-04 | Boston Scientific Neuromodulation Corporation | Leads containing segmented electrodes with non-perpendicular legs and methods of making and using |
| CN105263568A (en) | 2013-05-31 | 2016-01-20 | 波士顿科学神经调制公司 | Leads with segmented electrodes and methods of making the leads |
| US9149630B2 (en) | 2013-05-31 | 2015-10-06 | Boston Scientific Neuromodulation Corporation | Segmented electrode leads formed from pre-electrodes with alignment features and methods of making and using the leads |
| US9248272B2 (en) | 2013-05-31 | 2016-02-02 | Boston Scientific Neuromodulation Corporation | Segmented electrode leads formed from pre-electrodes with depressions or apertures and methods of making and using |
| US9265935B2 (en) | 2013-06-28 | 2016-02-23 | Nevro Corporation | Neurological stimulation lead anchors and associated systems and methods |
| EP3019232B1 (en) | 2013-07-12 | 2019-08-21 | Boston Scientific Neuromodulation Corporation | Leads with segmented electrodes and methods of making the leads |
| US9566747B2 (en) | 2013-07-22 | 2017-02-14 | Boston Scientific Neuromodulation Corporation | Method of making an electrical stimulation lead |
| WO2015031375A1 (en) | 2013-08-30 | 2015-03-05 | Boston Scientific Neuromodulation Corporation | Methods of making segmented electrode leads using flanged carrier |
| EP3077039B1 (en) | 2013-12-02 | 2021-10-13 | Boston Scientific Neuromodulation Corporation | Methods for manufacture of electrical stimulation leads with helically arranged electrodes |
| EP3476430B1 (en) | 2014-05-16 | 2020-07-01 | Aleva Neurotherapeutics SA | Device for interacting with neurological tissue |
| US11311718B2 (en) | 2014-05-16 | 2022-04-26 | Aleva Neurotherapeutics Sa | Device for interacting with neurological tissue and methods of making and using the same |
| WO2015192058A1 (en) | 2014-06-13 | 2015-12-17 | Boston Scientific Neuromodulation Corporation | Leads with electrode carriers for segmented electrodes and methods of making and using |
| US9959388B2 (en) | 2014-07-24 | 2018-05-01 | Boston Scientific Neuromodulation Corporation | Systems, devices, and methods for providing electrical stimulation therapy feedback |
| US10272247B2 (en) | 2014-07-30 | 2019-04-30 | Boston Scientific Neuromodulation Corporation | Systems and methods for stimulation-related volume analysis, creation, and sharing with integrated surgical planning and stimulation programming |
| US10265528B2 (en) | 2014-07-30 | 2019-04-23 | Boston Scientific Neuromodulation Corporation | Systems and methods for electrical stimulation-related patient population volume analysis and use |
| US9403011B2 (en) | 2014-08-27 | 2016-08-02 | Aleva Neurotherapeutics | Leadless neurostimulator |
| US9474894B2 (en) | 2014-08-27 | 2016-10-25 | Aleva Neurotherapeutics | Deep brain stimulation lead |
| US9925376B2 (en) | 2014-08-27 | 2018-03-27 | Aleva Neurotherapeutics | Treatment of autoimmune diseases with deep brain stimulation |
| US9770598B2 (en) | 2014-08-29 | 2017-09-26 | Boston Scientific Neuromodulation Corporation | Systems and methods for making and using improved connector contacts for electrical stimulation systems |
| EP3204112A1 (en) | 2014-10-07 | 2017-08-16 | Boston Scientific Neuromodulation Corporation | Systems, devices, and methods for electrical stimulation using feedback to adjust stimulation parameters |
| WO2016065345A1 (en) * | 2014-10-24 | 2016-04-28 | Medtronic, Inc. | Coronary sinus medical electrical lead |
| US9604068B2 (en) | 2014-11-10 | 2017-03-28 | Boston Scientific Neuromodulation Corporation | Systems and methods for making and using improved connector contacts for electrical stimulation systems |
| US9561362B2 (en) | 2014-11-10 | 2017-02-07 | Boston Scientific Neuromodulation Corporation | Systems and methods for making and using improved contact arrays for electrical stimulation systems |
| EP3229891B1 (en) | 2015-02-06 | 2019-08-14 | Boston Scientific Neuromodulation Corporation | Systems with improved contact arrays for electrical stimulation systems |
| WO2016164361A1 (en) | 2015-04-10 | 2016-10-13 | Boston Scientific Neuromodulation Corporation | Systems and methods for making and using improved contact arrays for electrical stimulation systems |
| WO2016182997A2 (en) | 2015-05-10 | 2016-11-17 | Alpha Omega Neuro Technologies, Ltd. | Automatic brain probe guidance system |
| US11234632B2 (en) | 2015-05-10 | 2022-02-01 | Alpha Omega Engineering Ltd. | Brain navigation lead |
| US11051889B2 (en) | 2015-05-10 | 2021-07-06 | Alpha Omega Engineering Ltd. | Brain navigation methods and device |
| CN107530542B (en) | 2015-05-26 | 2020-10-13 | 波士顿科学神经调制公司 | System for analyzing electrical stimulation and selecting or manipulating activation volume |
| US10780283B2 (en) | 2015-05-26 | 2020-09-22 | Boston Scientific Neuromodulation Corporation | Systems and methods for analyzing electrical stimulation and selecting or manipulating volumes of activation |
| US10441800B2 (en) | 2015-06-29 | 2019-10-15 | Boston Scientific Neuromodulation Corporation | Systems and methods for selecting stimulation parameters by targeting and steering |
| WO2017003946A1 (en) | 2015-06-29 | 2017-01-05 | Boston Scientific Neuromodulation Corporation | Systems and methods for selecting stimulation parameters based on stimulation target region, effects, or side effects |
| US9656093B2 (en) | 2015-07-16 | 2017-05-23 | Boston Scientific Neuromodulation Corporation | Systems and methods for making and using connector contact arrays for electrical stimulation systems |
| US9956394B2 (en) | 2015-09-10 | 2018-05-01 | Boston Scientific Neuromodulation Corporation | Connectors for electrical stimulation systems and methods of making and using |
| US10413737B2 (en) | 2015-09-25 | 2019-09-17 | Boston Scientific Neuromodulation Corporation | Systems and methods for providing therapy using electrical stimulation to disrupt neuronal activity |
| US10071249B2 (en) | 2015-10-09 | 2018-09-11 | Boston Scientific Neuromodulation Corporation | System and methods for clinical effects mapping for directional stimulation leads |
| US10328271B2 (en) | 2015-11-12 | 2019-06-25 | Medtronic, Inc. | Implantable electrical stimulator with deflecting tip lead |
| US10342983B2 (en) | 2016-01-14 | 2019-07-09 | Boston Scientific Neuromodulation Corporation | Systems and methods for making and using connector contact arrays for electrical stimulation systems |
| US10716942B2 (en) | 2016-04-25 | 2020-07-21 | Boston Scientific Neuromodulation Corporation | System and methods for directional steering of electrical stimulation |
| US10201713B2 (en) | 2016-06-20 | 2019-02-12 | Boston Scientific Neuromodulation Corporation | Threaded connector assembly and methods of making and using the same |
| AU2017281934B2 (en) | 2016-06-24 | 2019-11-14 | Boston Scientific Neuromodulation Corporation | Systems and methods for visual analytics of clinical effects |
| US10307602B2 (en) | 2016-07-08 | 2019-06-04 | Boston Scientific Neuromodulation Corporation | Threaded connector assembly and methods of making and using the same |
| US10350404B2 (en) | 2016-09-02 | 2019-07-16 | Boston Scientific Neuromodulation Corporation | Systems and methods for visualizing and directing stimulation of neural elements |
| US10780282B2 (en) | 2016-09-20 | 2020-09-22 | Boston Scientific Neuromodulation Corporation | Systems and methods for steering electrical stimulation of patient tissue and determining stimulation parameters |
| US10543374B2 (en) | 2016-09-30 | 2020-01-28 | Boston Scientific Neuromodulation Corporation | Connector assemblies with bending limiters for electrical stimulation systems and methods of making and using same |
| JP6828149B2 (en) | 2016-10-14 | 2021-02-10 | ボストン サイエンティフィック ニューロモデュレイション コーポレイション | Systems and methods for closed-loop determination of stimulation parameter settings for electrical stimulation systems |
| US10576269B2 (en) | 2017-01-03 | 2020-03-03 | Boston Scientific Neuromodulation Corporation | Force-decoupled and strain relieving lead and methods of making and using |
| WO2018128949A1 (en) | 2017-01-03 | 2018-07-12 | Boston Scientific Neuromodulation Corporation | Systems and methods for selecting mri-compatible stimulation parameters |
| ES2821752T3 (en) | 2017-01-10 | 2021-04-27 | Boston Scient Neuromodulation Corp | Systems and procedures for creating stimulation programs based on user-defined areas or volumes |
| US10905871B2 (en) | 2017-01-27 | 2021-02-02 | Boston Scientific Neuromodulation Corporation | Lead assemblies with arrangements to confirm alignment between terminals and contacts |
| WO2018160495A1 (en) | 2017-02-28 | 2018-09-07 | Boston Scientific Neuromodulation Corporation | Toolless connector for latching stimulation leads and methods of making and using |
| AU2018231031B2 (en) | 2017-03-09 | 2023-11-02 | Nevro Corp. | Paddle leads and delivery tools, and associated systems and methods |
| US10625082B2 (en) | 2017-03-15 | 2020-04-21 | Boston Scientific Neuromodulation Corporation | Visualization of deep brain stimulation efficacy |
| WO2018187090A1 (en) | 2017-04-03 | 2018-10-11 | Boston Scientific Neuromodulation Corporation | Systems and methods for estimating a volume of activation using a compressed database of threshold values |
| US10603499B2 (en) | 2017-04-07 | 2020-03-31 | Boston Scientific Neuromodulation Corporation | Tapered implantable lead and connector interface and methods of making and using |
| WO2019014224A1 (en) | 2017-07-14 | 2019-01-17 | Boston Scientific Neuromodulation Corporation | Systems and methods for estimating clinical effects of electrical stimulation |
| EP3658228A1 (en) | 2017-07-25 | 2020-06-03 | Boston Scientific Neuromodulation Corporation | Systems and methods for making and using an enhanced connector of an electrical stimulation system |
| WO2019036180A1 (en) | 2017-08-15 | 2019-02-21 | Boston Scientific Neuromodulation Corporation | Systems and methods for controlling electrical stimulation using multiple stimulation fields |
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Family Cites Families (12)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US164184A (en) * | 1875-06-08 | Improvement in vesicular electrodes | ||
| US932775A (en) * | 1909-06-05 | 1909-08-31 | Charles W Gaston | Electric therapeutic instrument. |
| US3804098A (en) * | 1972-04-17 | 1974-04-16 | Medronic Inc | Body implantable lead |
| CA1065969A (en) * | 1977-09-28 | 1979-11-06 | Gratien Bouillon | Self-blocking cerebral catheter |
| US4890623A (en) * | 1988-03-14 | 1990-01-02 | C. R. Bard, Inc. | Biopotential sensing device and method for making |
| FR2629710B1 (en) * | 1988-04-08 | 1997-10-24 | Mxm | ELECTRODE HOLDER DEVICES IMPLANTABLE IN THE COCHLEE FOR ELECTRICALLY STIMULATING THE HEARING NERVE |
| US5127403A (en) * | 1988-07-05 | 1992-07-07 | Cardiac Control Systems, Inc. | Pacemaker catheter utilizing bipolar electrodes spaced in accordance to the length of a heart depolarization signal |
| US4903702A (en) * | 1988-10-17 | 1990-02-27 | Ad-Tech Medical Instrument Corporation | Brain-contact for sensing epileptogenic foci with improved accuracy |
| US5358514A (en) * | 1991-12-18 | 1994-10-25 | Alfred E. Mann Foundation For Scientific Research | Implantable microdevice with self-attaching electrodes |
| GB9317099D0 (en) * | 1993-08-17 | 1993-09-29 | Medinnova Sf | Electrode assembly |
| US5464446A (en) | 1993-10-12 | 1995-11-07 | Medtronic, Inc. | Brain lead anchoring system |
| AU1837695A (en) * | 1994-02-09 | 1995-08-29 | University Of Iowa Research Foundation, The | Human cerebral cortex neural prosthetic |
-
1996
- 1996-09-27 US US08/721,816 patent/US5843148A/en not_active Expired - Lifetime
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1997
- 1997-09-22 CA CA002216021A patent/CA2216021C/en not_active Expired - Fee Related
- 1997-09-24 EP EP97307460A patent/EP0832667B1/en not_active Expired - Lifetime
- 1997-09-24 DE DE69727749T patent/DE69727749T2/en not_active Expired - Lifetime
- 1997-09-25 AU AU39237/97A patent/AU726391B2/en not_active Ceased
- 1997-09-26 JP JP9261249A patent/JPH10137346A/en active Pending
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| DE69727749D1 (en) | 2004-04-01 |
| EP0832667B1 (en) | 2004-02-25 |
| CA2216021A1 (en) | 1998-03-27 |
| AU3923797A (en) | 1998-04-02 |
| AU726391B2 (en) | 2000-11-09 |
| JPH10137346A (en) | 1998-05-26 |
| DE69727749T2 (en) | 2005-01-20 |
| EP0832667A3 (en) | 1999-11-24 |
| US5843148A (en) | 1998-12-01 |
| EP0832667A2 (en) | 1998-04-01 |
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| EEER | Examination request | ||
| MKLA | Lapsed |