|Publication number||US20050159799 A1|
|Application number||US 10/997,045|
|Publication date||Jul 21, 2005|
|Filing date||Nov 24, 2004|
|Priority date||Nov 25, 2003|
|Also published as||US8224456, US8571685, US20050171587, US20130013039, WO2005053789A2, WO2005053789A3|
|Publication number||10997045, 997045, US 2005/0159799 A1, US 2005/159799 A1, US 20050159799 A1, US 20050159799A1, US 2005159799 A1, US 2005159799A1, US-A1-20050159799, US-A1-2005159799, US2005/0159799A1, US2005/159799A1, US20050159799 A1, US20050159799A1, US2005159799 A1, US2005159799A1|
|Inventors||Terry Daglow, Sandy Hooper|
|Original Assignee||Advanced Neuromodulation Systems, Inc.|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (6), Referenced by (26), Classifications (5), Legal Events (1)|
|External Links: USPTO, USPTO Assignment, Espacenet|
This application claims benefit and priority (under 35 U.S.C. §119(e)) to prior U.S. provisional application Ser. No. 60/524,982 filed on Nov. 25, 2003, and which is incorporated herein by reference.
The present invention relates to electrical leads, percutaneous needles and methods of implanting such leads.
Implantable leads having electrodes are used in a variety of applications, including the delivery of electrical stimulation to surrounding tissue, neural or otherwise, as well as measuring electrical energy produced by such tissue. Some leads include lumens for the delivery of other elements, including chemicals and drugs. Whether in a stimulation, sensing or element delivery capacity, such leads are commonly implanted along peripheral nerves, within the epidural or intrathecal space of the spinal column, and around the heart, brain, or other organs or tissue of a patient.
Differing techniques have been utilized to construct or manufacture such leads. Some prior art leads and methods of manufacture have been disclosed in several United States patents, such as U.S. Pat. Nos. 5,016,646 (Gotthardt, et al.), 5,433,742 (Willis), 6,208,881 (Champeau) and 6,216,045 (Black, et al.), which are each incorporated herein by reference. One example of a directional brain stimulation and recording leads is disclosed in PCT publication WO 02/045795 (Jun. 13, 2002), which is incorporated herein by reference. A length of tubing having a window cut therein forms a sleeve insulating member (or formed by injection molding, vulcanization molding) that is placed over the distal end of the lead.
Generally, several elements (conductors, electrodes and insulation) are combined to produce a lead body. A lead typically includes one or more conductors extending the length of the lead body from a distal end to a proximal end of the lead. The conductors electrically connect one or more electrodes at the distal end to one or more connectors at the proximal end of the lead. The electrodes are designed to form an electrical connection or stimulus point with tissue or organs. Lead connectors (sometimes referred to as contacts, or contact electrodes) are adapted to electrically and mechanically connect leads to implantable pulse generators or RF receivers (stimulation sources), or other medical devices. An insulating material typically forms the lead body and surrounds the conductors for electrical isolation between the conductors and protection from the external contact and compatibility with a body.
Such leads are typically implanted into a body at an insertion site and extend from the implant site to the stimulation site (area of placement of the electrodes). The implant site is typically a subcutaneous pocket that receives and houses the pulse generator or receiver (providing a stimulation source). The implant site is usually positioned a distance away from the stimulation site, such as near the buttocks or other place in the torso area. In some cases, the implant site (and/or insertion site) is located in the lower back area, and the lead may extend through the epidural space (or other space) in the spine to the stimulation site (middle or upper back, or neck or brain areas). In other cases, the implant site may be located in the brain or other part of the body. In still other cases, the stimulation source may not be implanted, and may be external to the body.
Application of specific electrical fields to spinal nerve roots, spinal cord, deep brain stimulation, and other nerve bundles or tissue for the purpose of pain control has been actively practiced for years. While a precise understanding of the interaction between the applied electrical energy and the stimulated tissue is not fully appreciated, it is known that application of an electrical field to spinal or other tissue (e.g., spinal nerve roots and spinal cord bundles) can effectively mask certain types of pain transmitted from regions of the body associated with the stimulated tissue.
It is known that each exterior region, or each dermatome, of the human body is associated with a particular spinal nerve root at a particular longitudinal spinal position. The head and neck regions are associated with C2-C8, the back regions with C2-S3, the central diaphragm is associated with spinal nerve roots between C3 and C5, the upper extremities correspond to C5 and T1, the thoracic wall extends from T1 to T11, the peripheral diaphragm is between T6 and T11, the abdominal wall is associated with T6-L1, the lower extremities related to L2 to S2, and the perineum from L4 to S4. By example, to address pain sensations that commonly focus on the lower back and lower extremities, a specific energy field can usually be applied to a region between bony level T8 to T10. As should be understood, successful therapy management and the avoidance of stimulation in unafflicted regions generally requires the applied electric field to be properly positioned longitudinally along the dorsal column.
Therapy-managing electrical energy is commonly delivered through electrodes positioned at the desired stimulation site. The electrodes are generally carried by one of two types of leads: percutaneous and laminotomy (commonly referred to as “paddle” leads).
Percutaneous leads (including catheter types) are generally small in diameter and have a plurality of spaced electrodes. Percutaneous leads are typically placed within the body through the use of a Touhy-like needle. For insertion, the Touhy-like needle is passed through the skin at the desired location (insertion site) and the lead is inserted through the needle.
Laminotomy leads have a paddle configuration, and are generally larger than percutaneous leads, and typically possess a plurality of electrodes (for example, two, four, eight, or sixteen) arranged in one or more columns.
Laminotomy leads are generally used for applications in which is it desirous that the applied electrical energy (stimulation) be directional in nature, such as to address both unilateral and bilateral pain, where electrical energy may be administered using either column independently (on either side of the midline) or administered using both columns to create an electric field which traverses the midline. A multi-column laminotomy lead may enable reliable positioning of a plurality of electrodes, and in particular, provide a plurality of electrode columns that do not readily deviate from an initial implantation position/orientation.
However, laminotomy leads require a significant surgical procedure for implantation. The surgical procedure generally requires the resection and removal of certain tissue (vertebral tissue in the case of spinal applications) to allow both access to the dura and proper positioning of a laminotomy lead.
Percutaneous leads, in contrast, require a less-invasive implantation method, and with a plurality of electrodes, provide a user the ability to create almost any electrode array. However, prior art percutaneous leads generally have band-type electrodes whereby the electrical energy field radiates circumferentially and therefore the electrical energy may not be focused solely on the desired area. Although likely more stable during use and directional in nature, laminotomy leads require a more complicated surgical procedure for implantation and removal.
Notwithstanding the range of electric fields that are possible with conventional stimulation leads, in certain instances it is necessary to concentrate electrical energy at a particular point, or over a small region. As an example of such occasion, assume therapy-managing electrical energy is applied at or about T8 to address only localized lower back pain. At T8, spinal nervous tissue corresponding to the patient's lower extremities may also commingle with the specific spinal nervous tissue associated with the lower back. Since it is common that the lower back-related spinal nervous tissue is deeply embedded within the combined spinal nervous tissue, it becomes desirable to focus applied electrical energy to the targeted nervous tissue to (i) reach the deeply situated target nervous tissue and (ii) avoid undesirable stimulation of unafflicted regions, while avoiding surgical procedures for the lead(s) implantation and removal.
Accordingly, a need exists for a stimulation lead that includes a structural arrangement that facilitates directional concentration of delivered electrical energy at a point, i.e., for a given electrode, or over a small region, i.e., for a plurality of electrodes, and at the same time, may be implanted (and/or removed) without significant surgical procedure.
Additionally, implantation of leads using percutaneous methods involves the insertion of the lead into the body via a needle used as a passageway into the body. During the insertion procedure, the lead is pushed (forward) into the body, and in some occasions, there is a need for the lead to be pulled back (partly or completely) through the needle. This problem is described further by reference to
Accordingly, there exists a need for a needle for use in percutaneous insertions which reduces the likelihood that, when an inserted lead is pulled back through the needle, the lead could be damaged.
In accordance with the present invention, there is provided a needle for percutaneous insertion of a device. The needle includes a body having a proximal end and a distal end, and an introducer portion at the distal end and having an orifice, the introducer portion including a flared portion proximate a heel of the body.
In another embodiment of the present invention, there is provided a percutaneous insertion needle including an elongated body having a passage extending from a proximal end portion to a distal end portion of the needle, and an introducer portion at the distal end portion and adjacent a body portion of the body, the introducer having an orifice and a heel portion, the heel portion including a lip portion, and wherein the cross section area of the lip portion is greater than a cross section area of the adjacent body portion.
In yet another embodiment of the present invention, there is provided a method of placing a lead in a body. The method includes providing a needle including a body having a proximal end and a distal end, and an introducer portion at the distal end and having an orifice, the introducer portion including a flared portion proximate a heel of the body. The method further includes percutaneously accessing a site within the body proximate to a desire lead placement location in the body using the needle and directing the lead through the needle into the site.
In still another embodiment of the invention, there is provided a system for treating neurological disorders. The system includes a source for generating a stimulus and an implantable lead for receiving the stimulus from the source. A needle for percutaneous insertion of the lead includes a body having a proximal end and a distal end, and an introducer portion at the distal end and having an orifice, the introducer portion including a flared portion proximate a heel of the body.
For a more complete understanding of the present invention, and the advantages thereof, reference is now made to the following descriptions taken in conjunction with the accompanying drawings, wherein like numbers designate like objects, and in which:
With reference to
As will be appreciated, any number of conductors 26, electrodes 18 and contact electrodes 20 may be utilized, as desired. For purposes of illustration only, the lead 10 is shown with four contact electrodes 20 and four electrodes 18. It will be further understood that the distal end 14 of the lead 10 is shown with electrodes 18 as described further below. In addition, other types, configurations and shapes of contact electrodes 20 (and lead connectors) as known to those skilled in the art may be used, as desired.
Typically, the lead body 12 is a structure having a round cross-section. Alternatively, the cross-section of the lead body 12 may be configured in any number of cross-sectional shapes appropriate for the specific application. The figures and following description generally refer to a round cross-sectional shape for the lead body 12 for illustrative purposes only. The lead body 12 generally includes a lead body insulator 22 configured to insulate the conductors 26 and presents a biocompatible external surface to the body tissue. In one embodiment, the lead body insulator 22 is coextensive with the conductors 26.
The lead body insulator 22 is formed of insulating material typically selected based upon biocompatibility, biostability and durability for the particular application. The insulator material may be silicone, polyurethane, polyethylene, polyamide, polyvinylchloride, PTFT, EFTE, or other suitable materials known to those skilled in the art. Alloys or blends of these materials may also be formulated to control the relative flexibility, torqueability, and pushability of the lead 10. Depending on the particular application, the diameter of the lead body 12 may be any size, though a smaller size is more desirable for neurological and myocardial mapping/ablation leads and neuromodulation and stimulation leads.
The conductors (not shown) may take the form of solid wires, drawn-filled-tube (DFT), drawn-brazed-strand (DBS), stranded wires or cables, ribbons conductors, or other forms known or recognized to those skilled in the art. The composition of the conductors may include aluminum, stainless steel, MP35N, platinum, gold, silver, copper, vanadium, alloys, or other conductive materials or metals known to those of ordinary skill in the art. The number, size, and composition of the conductors will depend on the particular application for the lead 10, as well as the number of electrodes.
The conductors may be configured along the lead body 12 in a straight orientation or spirally or helically wound about the lumen 24 or center of the lead body 12. The conductors are typically insulated from the lumen 24, from each other, and from the external surface of the lead 10 by the insulative material 22. The insulative material 22 may be of a single composition, or multiple layers of the same or different materials.
At least one electrode 18 is positioned at the distal end 14 of the lead body 12 for electrically engaging a target tissue or organ. In addition, at least one connector 20 is positioned at the proximal end 16 of the lead body 12 for electrically connecting the conductors 26 to a stimulating or receiving source. In one embodiment, the lead 10 is generally configured to transmit an electric signal from an electrical source (see
The electrodes 18 and contact electrodes 20 are typically made of a conductive material such as platinum, gold, silver, platinum-iridium, stainless steel, MS35N, or other conductive materials, metals or alloys known to those skilled in the art. The size of the electrodes 18 is generally chosen based upon the desired application. The contact electrodes 20 generally have a size and configuration appropriate to connect the lead 10 to a desired electrical source or receiver.
With reference to
With respect to both embodiments shown in
The location and shape of the openings 52 in the insulating member 50 mask a portion of the electrodes 18 and function to limit the electrical energy that is transmitted from each of the electrodes 18 when activated (stimulus) and/or to direct the energy in a desired direction. The energy from the electrodes 18 (or electrode array) can be focused in a limited direction less than the typical 360 degrees associated with band electrodes (a length along the circumference and longitudinal length may be desired, and in one embodiment, about 10 to 180 degrees of the circumference is possible, with about 45 or 90 degrees preferred).
As illustrated in
As is known in the art, following implantation in the spinal area, tissue will grow around the electrode (paddle or percutaneous lead) and will usually increase the impedance associated with the electrode, thus reducing its ability to electrically couple with the targeted tissue. In order to maintain a constant or adequate degree of stimulation, it may be necessary to increase the energy delivered as the impedance increases. This creates the risk of stimulating or over-stimulating areas that are not intended to be stimulated. One typical solution to this problem has been to use a paddle lead, however, a paddle lead is large and is not percutaneously implanted, therefore requires significant surgical procedure and is guided to the target area. Additionally it is not appropriate in certain applications, such as for brain stimulation leads.
The directional or unidirectional lead 10 provided by the present invention is a percutaneous lead that directs the energy array of the electrode in a specified or desired direction. With this ability, a clinician can target a small area of nerves for stimulation without the danger of over-stimulation of non-targeted nerves or other nearby tissues.
The present invention provides a percutaneous lead capable of directionally sending energy from the lead. The directional capability of this lead is derived from the fact that part of the electrode(s) associated with the lead is masked by insulative material. Stimulation energy from the electrode array can be focused in a desired (and/or limited) direction (or specific area or point) that is less than 360 degrees (as measured circumferentially). The present invention lead has the same uses as traditional paddle leads, but may be smaller in size and shape. The directional lead is typically the same size and shape as a traditional percutaneous lead. With this in mind, it is possible to implant the lead using the same techniques used to implant traditional percutaneous leads via needle. Thus, the present invention lead provides a percutaneous lead having selective directional stimulation. As will be appreciated, use of two or more leads having a directional nature allow the electric fields to be directed between the two leads to more effectively stimulate the targeted tissue while avoiding excess stimulation of other structures.
With regards to the embodiments shown in
With reference to
With reference to
At a step 336, the insulating member or insulating layer 50 b is formed over the electrodes 18 b (see
Alternatively, the lead of step 330 may include the electrodes, and the removing step 332 may further include removing a layer of the insulative material and a similar outer layer of the electrode(s). In this embodiment, the step 334 would be omitted.
In one embodiment, the insulating member or layer 50 a, 50 b is made of any suitable insulative material sufficient to substantially prevent or substantially reduce electrical radiation from the electrodes 18 a, 18 b. In another embodiment, the insulating member or layer 50 a, 50 b is composed of paralyne. Thicknesses of the insulating member or layer 50 a, 50 b can range from 0.0005 to 0.002 inches, and is preferable in the range of 0.0005 to 0.0009 inches, and may be about 0.0007 inches. The insulative member or layer 50 a, 50 b may be formed in the forming step 302, 336 by various methods, including chemical or physical vapor deposition, sputtering, thermal growth, etc.
In one embodiment, the insulating member or layer 50 a, 50 b is formed over the entire portion of each electrode 18 a, 18 b and, subsequently, a selected portion (the portion desired to be exposed) of the insulating member 50 a, 50 b is removed to form the openings 52 a, 52 b. Different techniques may be utilized to form the openings 52 a, 52 b, including laser ablation, etching, cutting, or similar and like methods sufficient to remove a selected portion and expose the electrode 18 a, 18 b. In another embodiment, masking material (or a masking layer) (not shown) is used to selectively mask the portion of the electrode 18 a, 18 b desired to be exposed. The insulating member/layer 50 a, 50 b is formed on the distal end 14, and the masking material/layer is removed to expose the electrode 18 a, 18 b.
Additionally, the insulating member or layer 50 may be applied by insert-molding, coating followed by etching, scribing or cutting to define the windows 52, or selective vapor deposition of insulative materials to form a patterned layer that defines one or more windows 52.
In the embodiment shown in
With reference to
As shown in
The marker 600 is tubular in shape and resembles a band electrode. The notch 602 of the marker 600 typically extends circumferentially with the lead body for a predetermined distance or arc. In the embodiment shown, the notch 602 extends arcuately for a length equal to about 180 degrees (about one-half way around), or a 180 degree arc. In other embodiments, any length/arc may be chosen sufficient to provide the functionality described herein, including ranging from 90 degrees to 270 degrees or forty-five degrees. Moreover, the axial length of the marker 600 may be any desired length sufficient to obtain the desired results, but is typically about the same or shorter than axial length of the electrodes 18.
To function effectively as a marking or orientation system for orienting/positioning the lead within a body for directional stimulation, the notch (or the portion “non-visible” via fluoroscopy or X-ray) 602 of the marker 600 is oriented or fixed in a predetermined relation with respect to the exposed portions of the electrodes 18. As will be appreciated, depending on the shape and directional orientation of the electrodes 18 (exposed portions), and the marker 600 (notch), the marker 600 and electrodes 18 are fixed generally at a circumferential distance from each other. In the example illustrated in
While any offset positioning may be used, it appears that an offset of ninety degrees (plus or minus) may be more effective, as it is easier to view and comprehend such relative positioning with respect to two components.
Now with reference to
Those of ordinary skill in the art will readily understand that, when the lead with the marker 602 of the present invention is implanted, the marker silhouette viewable through utilization of a detecting device (e.g., fluoroscope or X-ray device) will show different configurations depending on the orientation of the lead. For example, assuming the notch size is approximately one-half the band, when the notch is facing directly toward or away from the detecting device, a complete band will be visible. Similarly, if facing directly perpendicular to the detecting device, the visible configuration will provide information as to the orientation of the lead (i.e. a C-shape). Therefore, the marker 600 will allow a clinician the ability to orient the lead in a fashion so as to direct the stimulation in a desired direction (using the directional electrodes).
The marker 600 is capable of recognition in the body through the use of a fluoroscope, radiation, or other similar or like technology. This allows a medical professional to determine the orientation of the directional electrodes of the lead relative to the targeted tissue. The marker(s) band within the lead allows a medical professional to quickly and easily determine the relative position of the electrode(s) 18 a, 18 b within lead 10 (see
As will be appreciated, more than one marker 602 (not shown) may be optionally utilized. Further, the sizes, shapes and configurations of the marker 600 and the notch 602 may vary. While the embodiment of the marker 600 in
It will be understood by those skilled in the art that the marking or orientation system may include a single marker, or multiple markers, each of the marker(s) having some recognition attribute (recognizable by some means). Such recognition attributes include radio-opaque or radiopaic and structural (e.g., notch or groove), and the system may utilize multiple markers each utilizing a different attribute to create a marking system for orienting the implanted lead (or simply for determining the orientation).
One characteristic of the embodiment shown in
However, even with leads having substantially the same outer diameter, prior art percutaneous insertion leads will tend to cut or damage a lead when it is pulled back through the needle.
Now with reference to
With reference to
Now referring to
As described above, the configuration of the heel edge of the needle 800 as shown by the lip or flare section 812 helps reduces the likelihood that a lead/catheter inserted through the needle 800 (extending through the orifice 808) will become cut or damaged in the event the lead/catheter is pulled back through the needle toward the proximal end of the needle.
An orifice edge of the introducer section 808 further includes a radius of curvature R2 of approximately 0.05 inches.
In one embodiment of an implantable procedure, a small incision is first made in a body using a scalpel at the desired site of insertion. Making an initial incision prevents the application of excess force to the tip of the needle 800 and further avoids the undesirable introduction of dermal matter into the location. The needle 800 is introduced through the incision at an angle that allows passage of the needle 200 between vertebral bodies. Once the distal end 810 of the needle 200 is positioned within and opens into the desired location (typically, epidural space), a lead is inserted.
Now referring to
As shown in
As shown in
The wireless receiver (not shown) within stimulation source 310 is capable of receiving wireless signals from a wireless transmitter 320. The wireless signals are represented in
As will be appreciated, the contact electrodes 20 are not visible in
It may be advantageous to set forth definitions of certain words and phrases that may be used within this patent document: the terms “include” and “comprise,” as well as derivatives thereof, mean inclusion without limitation; the term “or,” is inclusive, meaning and/or; the phrases “associated with” and “associated therewith,” as well as derivatives thereof, may mean to include, be included within, interconnect with, contain, be contained within, connect to or with, couple to or with, be communicable with, cooperate with, interleave, juxtapose, be proximate to, be bound to or with, have, have a property of, or the like; and if the term “controller” is utilized herein, it means any device, system or part thereof that controls at least one operation, such a device may be implemented in hardware, firmware or software, or some combination of at least two of the same. It should be noted that the functionality associated with any particular controller may be centralized or distributed, whether locally or remotely.
Although the present invention and its advantages have been described in the foregoing detailed description and illustrated in the accompanying drawings, it will be understood by those skilled in the art that the invention is not limited to the embodiment(s) disclosed but is capable of numerous rearrangements, substitutions and modifications without departing from the spirit and scope of the invention as defined by the appended claims.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US5054492 *||Dec 17, 1990||Oct 8, 1991||Cardiovascular Imaging Systems, Inc.||Ultrasonic imaging catheter having rotational image correlation|
|US5456254 *||Apr 5, 1994||Oct 10, 1995||Cardiac Pathways Corp||Flexible strip assembly having insulating layer with conductive pads exposed through insulating layer and device utilizing the same|
|US6205361 *||Jan 28, 1999||Mar 20, 2001||Advanced Bionics Corporation||Implantable expandable multicontact electrodes|
|US6309401 *||Apr 30, 1999||Oct 30, 2001||Vladimir Redko||Apparatus and method for percutaneous implant of a paddle style lead|
|US6375664 *||Jul 28, 1997||Apr 23, 2002||Dr. Japan Co., Ltd.||Mandrin of medical anesthetic needle and method of manufacturing same|
|US6505082 *||Aug 21, 2000||Jan 7, 2003||Cardiac Pacemakers, Inc.||Single pass lead system|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US7337005||Sep 7, 2005||Feb 26, 2008||Spinal Modulations, Inc.||Methods for stimulating a nerve root ganglion|
|US7337006||Sep 7, 2005||Feb 26, 2008||Spinal Modulation, Inc.||Methods and systems for modulating neural tissue|
|US7447546||Sep 7, 2005||Nov 4, 2008||Spinal Modulation, Inc.||Methods of neurostimulating targeted neural tissue|
|US7450993||Sep 7, 2005||Nov 11, 2008||Spinal Modulation, Inc.||Methods for selective stimulation of a ganglion|
|US7502651||Sep 7, 2005||Mar 10, 2009||Spinal Modulation, Inc.||Methods for stimulating a dorsal root ganglion|
|US7580753||Sep 7, 2005||Aug 25, 2009||Spinal Modulation, Inc.||Method and system for stimulating a dorsal root ganglion|
|US7941227||Sep 3, 2008||May 10, 2011||Boston Scientific Neuromodulation Corporation||Implantable electric stimulation system and methods of making and using|
|US8024049 *||Oct 20, 2004||Sep 20, 2011||University Of Central Florida Research Foundation, Inc.||Spatial-temporal deep brain stimulation methods and systems|
|US8032231 *||Oct 5, 2007||Oct 4, 2011||University Of Central Florida Research Foundation, Inc.||Spatial temporal deep brain stimulation methods and systems|
|US8082039||Sep 7, 2005||Dec 20, 2011||Spinal Modulation, Inc.||Stimulation systems|
|US8229565||Feb 11, 2009||Jul 24, 2012||Spinal Modulation, Inc.||Methods for stimulating a dorsal root ganglion|
|US8380318||Mar 24, 2010||Feb 19, 2013||Spinal Modulation, Inc.||Pain management with stimulation subthreshold to paresthesia|
|US8473073 *||May 30, 2010||Jun 25, 2013||Arnold B. Vardiman||Various apparatus and methods for deep brain stimulating electrodes|
|US8583257 *||May 30, 2010||Nov 12, 2013||Arnold B. Vardiman||Various apparatus and methods for deep brain stimulating electrodes|
|US8666507 *||May 30, 2010||Mar 4, 2014||Arnold B. Vardiman||Various apparatus and methods for deep brain stimulating electrodes|
|US8670837 *||May 26, 2011||Mar 11, 2014||Khosrow Daneshvar||Method and means to adjust the positioning of stimulating neural and muscular electrode|
|US8712546||Mar 19, 2008||Apr 29, 2014||Spinal Modulation, Inc.||Neurostimulation system|
|US8849408||Jan 4, 2013||Sep 30, 2014||University Of Central Florida Research Foundation, Inc.||Methods for electronic directionality of deep-brain stimulation|
|US8968299||Oct 10, 2007||Mar 3, 2015||St. Jude Medical, Atrial Fibrillation Division, Inc.||Circuit for a catheter or sheath and method of forming same|
|US9044592||Jan 29, 2008||Jun 2, 2015||Spinal Modulation, Inc.||Sutureless lead retention features|
|US9056197||Oct 27, 2009||Jun 16, 2015||Spinal Modulation, Inc.||Selective stimulation systems and signal parameters for medical conditions|
|US20090254078 *||Apr 10, 2009||Oct 8, 2009||Just Dale E||Ablation electrode and catheter assembly for epicardial mapping and ablation with directionally focused rf energy|
|US20100298908 *||May 30, 2010||Nov 25, 2010||Vardiman Arnold B||Various Apparatus and Methods for Deep Brain Stimulating Electrodes|
|US20100298917 *||May 30, 2010||Nov 25, 2010||Vardiman Arnold B||Various Apparatus and Methods for Deep Brain Stimulating Electrodes|
|US20100298918 *||May 30, 2010||Nov 25, 2010||Vardiman Arnold B||Various Apparatus and Methods for Deep Brain Stimulating Electrodes|
|US20120029590 *||Feb 2, 2012||Khosrow Daneshvar||Method and means to adjust the positioning of stimulating neural and muscular electrode|
|Cooperative Classification||A61N1/0551, A61N1/0529|
|Feb 28, 2005||AS||Assignment|
Owner name: ADVANCED NEUROMODULATION SYSTEMS, INC., TEXAS
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:DAGLOW, TERRY;HOOPER, SANDY M.;REEL/FRAME:016327/0692;SIGNING DATES FROM 20041123 TO 20041214