US3646940A - Implantable electronic stimulator electrode and method - Google Patents

Implantable electronic stimulator electrode and method Download PDF

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US3646940A
US3646940A US841756A US3646940DA US3646940A US 3646940 A US3646940 A US 3646940A US 841756 A US841756 A US 841756A US 3646940D A US3646940D A US 3646940DA US 3646940 A US3646940 A US 3646940A
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electrically
pulse
electrode
tissue
pulses
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Gerald W Timm
William E Bradley
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University of Minnesota
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    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00Electrotherapy; Circuits therefor
    • A61N1/18Applying electric currents by contact electrodes
    • A61N1/32Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/36007Applying electric currents by contact electrodes alternating or intermittent currents for stimulation of urogenital or gastrointestinal organs, e.g. for incontinence control

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  • the apparatus includes a plurality of electrodes, each of the electrodes including a pair of conductors [52] US. Cl ..l28/42l, 128/418 f carrying i l f positive and negative polarity, each f [51] Int. Cl.
  • This invention relates to apparatus and method for artificially and electrically stimulating masses of electrically excitable tissue. More specifically, this invention relates to an apparatus and method for electrically stimulating tissue in those persons who have lost the voluntary neural control of this excitable mass because of injury or disease, such as for example, loss of bladder function due to spinal cord injury.
  • Previous methods and apparatus of stimulating large tissue masses exhibit a disadvantage in that additive fields in the vicinity of the stimulated muscle can still occur owing to the parallel connection of multiple electrodes. That is, by the simultaneous application of a plurality of electrical fields resulting from the application of equal voltages to each of the electrodes, there will be generated at various points in the stimulated muscle, electrical fields that are greater than the individual fields resulting from each of the electrodes. Since the surrounding muscle tissue of concern often contains rapidly accommodating nerve fibers with low stimulus thresholds, these increases in field strength can be sufiicient to cause undesired muscle fiber stimulation.
  • this invention comprises a method and apparatus for locally stimulating masses of electrically excitable tissue in the presence of other excitable physiologic structures.
  • muscle will often be used generically to cover all masses of electrically excitable tissue structures.
  • the apparatus developed includes circuitry for providing nonsimultaneous or sequentially timed electrical impulses to various portions of the excitable mass.
  • a plurality of electrodes are electrically coupled to the mass, for instance the detrusor muscle of a urinary bladder, for providing electrical stimulation to the neural conducting system innervating the muscle in response to the application of electrical energy to individual ones of the electrodes.
  • Clocking and gating circuits are used for controlling the time and sequence of application of electrical impulses to the electrodes in a manner such that only one electrode is energized at any given time.
  • specially formed electrodes are utilized. These electrodes are bipolar in construction and are arranged to have a plurality of electrically conductive connection points for coupling to the muscle at a plurality of positions. Insulation is provided for electrically isolating the electrodes from contiguous muscle structures that might receive undesired stimulations.
  • Urinary sepsis secondary to neurogenic dysfunction associated with spinal cord trauma has been recognized as a clinical problem. Further, it has been recognized that prolonged use of indwelling catheters in paraplegic patients produces significant bacteriuria, cystitis, vesical calculi, and
  • Bladder tonus or the response of the bladder smooth muscle to the stretch imposed by filling, has been described as anintrinsic property of smooth muscle and not reflex in nature. Changes in this response are shown to follow physical alteration in the bladder tissue. Regular, complete evacuation of the neurogenic bladder with avoidance of inflection and damage, is therefore an aid in preserving normal tonus and facilitating rehabilitation of bladder function. Electrical excitability of the mammalian bladder has been demonstrated. Further, various forms of implantable muscle or bladder stimulators have been described, as indicated by U.S. Pat. No. 3,236,240.
  • Still another object of this invention is to provide a passive internal bladder muscle stimulator adapted to be implanted subcutaneously and being provided with electrodes which are electrically attached to the bladder muscle, wherein the stimulator derives its properly timed stimulation power for each of the electrodes from an external high-power radiofrequency transmitter.
  • Yet a further object of this invention is to provide an implantable muscle stimulator that is so operated in a nonsimultaneous manner of activation of a plurality of electrodes, and is so insulated, that contiguous tissue structures to which the electrodes are coupled are not stimulated.
  • the stimulator provides nonsimultaneous impulses to a plurality of electrodes by way of output circuits electrically isolated and arranged so that current flow between the output circuits is prevented thereby preventing the generation of massive current fields between the electrodes.
  • FIG. 1 is a perspective view of an internal implantable stimulator according to the present invention
  • FIG. 3 illustrates a type of bipolar electrode design utilizing two coils of conductor and having a plurality of electrical interconnection points
  • FIG. 4 illustrates a characteristic placement of electrodes on a urinary bladder, with two electrodes near the lateral ligaments on the ventral surface and one electrode on the caudalrostral midline of the dorsal surface;
  • FIG. 5 illustrates a method of electrically connecting an electrode into the depth of a muscle structure, and illustrates the insulating backing for providing electrical isolation of stimuli from contiguous excitable structures surrounding a muscle;
  • FIG. 6 is a schematic block circuit diagram of an implantable muscle stimulator deriving its stimulation power from an external power transmitter, and having clocking and pulse circuits for applying electrical impulses to only one electrode at a time;
  • FIG. 7 is an alternative embodiment of the invention, and is a schematic block circuit diagram of an implantable muscle stimulator utilizing a separate power source and pulse circuit for each bipolar electrode with isolating clock circuitry for determining the pulse application sequence so that only one electrode is energized at any instant of time;
  • FIG. 8 is a plot of a characteristic muscle pressure response derived from the simultaneous application of a plurality of electrical impulses.
  • FIG. 9 is a characteristic plot of pressure response obtained from a muscle having a plurality of electrical impulses sequentially applied.
  • the implantable stimulator comprises a receiver, indicated generally at 10, and a plurality of bipolar electrodes 11 for attachment to the muscle.
  • the electrodes 11 are connected to the receiver 10 by electrical conductors 12.
  • the receiver I0 is encased in a protective mass 13, preferably sterilizable, inert, nonirritating and nontoxic protective material, for example composed of a synthetic resinous material.
  • the conductors 12 are similarly encased in protective sheets 14, shown foreshortened to expose the conductive wires 12.
  • the electrodes 11 are bipolar and receive voltage signals VI through Vn respectively.
  • Each of the electrodes 11 is adapted for coupling to a pair of lines 12, with one of the lines 12 being designated and others of the line 12 being designated.
  • the invention embodies a method and apparatus for applying electrical stimuli to large masses of excitable muscle tissue without current spread to excitable tissue contiguous to the muscle to be stimulated.
  • the stimuli are applied through the multiple bipolar electrodes 11 with the two poles of each electrode being electrically isolated from any of the poles of the other electrodes.
  • the stimuli are developed in a manner whereby only one electrode has a voltage applied between its poles at any given time. In this regard, attention is directed to FIG. 2.
  • voltage pulses are applied to the bipolar electrodes in a nonsimultaneous or ordered manner so that additive stimulus fields are prevented.
  • voltage along the vertical axis is plotted versus time along the horizontal axis, with the time being expressed in groupings of milliseconds.
  • the bipolar electrode is referred to generally as 11, with the leads being designated 12+ and 12. It has been determined electrode 11 of this design is especially efficient for providing a stimulus current over an adequate mass and at a sufiicient depth in the detrusor muscle to activate the neural conduction system innervating it.
  • the conductors 12+ and 12- are fashioned from flexible coils or wires of Platinum-Iridium (Pt-Ir) wire or other suitable implantable conductor such as carbon-impregnated cloth, etc.
  • the conductors 12+ and 12- may be constructed from other metals such as tantalum, gold, silver, and alloys of these metals with other metals.
  • the receiver 10 components are encased or embedded in a sterilizable, inert, nonirritating and nontoxic protective insulating mass 13, preferably of a synthetic resinous material, with only the conductors 12 leading to the muscle stimulating electrodes 1 1 extending therefrom.
  • These conductors 12 are insulated by encasing them in a similar synthetic resinous protective and insulating material, or by coating them with a similar substance.
  • Substances which operate both for the stimulator l0 and the wires 12, with the desired insulating characteristics are silicone rubber, silastic resins, tetrafiuoroethylene polymers, vinyl chloride and the like, and are suitable materials for these purposes. Pure natural rubber may also be used.
  • a first plurality of conductive tabs 16 may be electrically connected to the wire 12+, and a second plurality of tabs 18 may be electrically coupled to wire 12- for ease of connection.
  • Each of the tabs contains an aperture for use in fastening the electrode 11 to the muscle. This will be described in more detail below.
  • These tabs 16 and 18 are constructed of the same material as the conductors 12+ and l2. The distances D1 and D2 can be varied and adjusted to accommodate different muscle sizes. It should be noted also that greater or fewer numbers of tabs 16 and 18 can be utilized both in parallel or in series with the conductors 12+ and 12. Further, for any particular muscle stimulation, the number of tabs and electrical interconnections may vary among the various electrodes 11.
  • Electrodes may be successfully employed in connection with the present invention.
  • various areas of electrical insulation may be bared from the conductor surface, and the electrodes effectively coupled to the tissue in this fashion.
  • FIG. 3 of the drawings a single electrode is illustrated, and it will be appreciated that two, three, or more electrodes may be utilized, and may be energized in sequential order, or may be energized as multiple pairs. In some instances, it may be desirable to utilize relatively large grid patterns which include a substantial number of individual electrode elements.
  • FIG. 4 A characteristic placement when three electrodes 11 are used is illustrated in FIG. 4 on a bladder 20.
  • the electrode 11 supplied with energy source V1 is applied at the caudal-rostral midline of the dorsal surface, shown in dashed line, and the two electrodes 1 1 energized by sources V2 and V3, are placed near the lateral ligaments on the ventral surface.
  • the number of attachment points can be varied to accommodate different sized bladders 20.
  • the ventral electrodes each utilize six tabs, whereas the single dorsal electrode utilizes eight tabs.
  • bladders of approximately ISO to 300 cc. capacities can be accommodated. Additional electrodes 11 may also be added to stimulate larger bladders.
  • FIG. 5 there is shown a sectional view of a portion of the bladder muscle 20, together with a portion of an electrode 1 I. Only the 12+ wire together with the 14+ insulation is shown. in this arrangement, there are three tabs 16, each having wires or thread 22 sewn through the apertures therein and for a predetermined depth into the muscle. In this arrangement, the wires 22 are metal sutures, and are inserted approximately 2 to 3 millimeters into the bladder wall and tied to the holes in tabs 16. This arrangement provides for electrical contact from the conductor 12+ into the detrusor muscle.
  • the electrodes 11 so designed and attached were made of a flexible design to follow the contour of the bladder during micturition.
  • the wires 22 can be of the same material as the electrode wires 12+ and l2, or other suitable electrically conductive materials.
  • a thin sheet of insulating material for instance, silastic, is placed over the electrodes to prevent stimulation of contiguous excitable structures.
  • this insulation is represented in cross section as element 24, and characteristically, can be in the order of 0.005 inch in thickness.
  • FIG. 6 a schematic block circuit diagram of an implantable muscle stimulator deriving its stimulation power from an external transmitter.
  • the portion of the stimulator shown enclosed within dashed block 30 includes a tuned resonant circuit 32, which characteristically can be comprised of an inductor and a capacitor in a parallel-connected resonant circuit.
  • a tuned resonant circuit 32 has the ability to store energy for short periods of time and tends to act as an energy reservoir.
  • the inductor of the tuned circuit 32 acts as an antenna, for picking up pulses of radiofrequency energy from an external highpower transmitter of conventional design (not shown), where such energy is transmitted through layers of body tissue to the tuned circuit 32.
  • the tuned circuit 32 is coupled to a circuit identified as rectifiers and filters 34 as indicated by arrow 36.
  • the signals provided by the tuned resonant circuit 32 are rectified into DC signals by filtering out the radiofrequency and the DC voltage so developed is applied at the output of the rectifiers and filters 34.
  • the signals are directed on lines 38 to clocking and pulse circuits 40 wherein the signals applied from lines 38 are converted to pulses and are alternatively applied to lines 42, 44, and 46 in substantially nonsimultaneous order.
  • the signals provided on lines 38 are converted to pulses by means of pulse generators, or multivibrators, of types available commercially, and these pulses are applied to the bipolar electrodes 42, 44, and 46 for durations determined by the clocking circuitry.
  • the clocking circuitry can be selected from various types of circuit components and arrangements well known in the prior art. Isolation elements 11, labeled 48; I2 labeled 50; and In labeled 52, are provided for isolating the electrodes electrically. Such isolation between electrodes can be provided for example by isolation transformers, or by simple diode arrangements for performing isolation as is well known. The signals provided from the isolation elements are taken directly to the electrodes with the wires being indicated by reference numeral 12, as previously used. It can be seen that the function of the clocking and pulse circuits 40 is to provide a planned application of signals to the isolation elements 48, 50, and 52 in a manner similar to that illustrated in FIG. 2. Only one of the bipolar lines 12 will carry signals at any given time.
  • FIG 7, An alternative embodiment is illustrated in FIG 7, wherein there is shown in schematic block diagram form an alternative implantable muscle stimulator 10.
  • a plurality of power sources indicated as PS1 labeled 54; PS2 labeled 56; and PSn labeled 58 is utilized, with a separate one of the power sources used for each of the bipolar electrodes 11.
  • a plurality of pulse generators with pulse generator 1, labeled 60, being coupled by line 62 to power source PSI.
  • pulse generator 2, labeled 64 is coupled by lines 66 to power source PS2.
  • pulse generator n, labeled 68 is coupled by lines 70 to PSn.
  • the output signals from the pulse generators 60, 64 and 68 are controlled by the clock circuit 72 respectively.
  • a clock circuit 72 can be any well-known isolating clock circuitry, such as ring counters, or the like, used to determine the pulse enabling sequence to each of the electrodes.
  • the output line 74 from clock circuit 72 controls pulse generator 1
  • a signal on line 76 controls pulse generator 2,7
  • the signal on line 78 controls pulse generator n.
  • the output signals from the pulse generators 60, 64 and 68 are applied on lines 12 in a nonsimultaneous arrangement as described above. It is readily apparent that the duration of the pulses occurring on lines 74, 76 and 78 determine the duration d of the power pulses in conjunction of the availability of energy signals on lines 62, 66 and 70, respectively.
  • the time duration between occurrences of signals on lines 74, 76 and 78 will determine the elapsed time between the activating pulses available on lines 12. Further, the duration of the count in clock circuit 72 until it completes the cycle will determine the duration d between consecutive signals on any given line V1, V2, and Vn.
  • FIG. 8 there is illustrated on characteristic pressure response curve for the situation wherein a muscle is stimulated by the simultaneous occurrence of three electrical signals. Application thereby indicating that only partial voiding of the bladder has occurred.
  • M denotes micturition.
  • FIG. 9 illustrates a characteristic pressure response obtained in a bladder wherein pulses were applied nonsimultaneously through three electrodes as described above. In this operation, it can be seen that the intravesical pressure rise upon stimulus S application led to a more complete bladder evacuation as indicated by a drop in residual pressure following the termination of the application of the stimulus S. Again, M denotes micturition.
  • Sequencing results in decreases in the field at the point, with this decrease being realized when changing from simultaneous to nonsimultaneous stimulus application.
  • a further decrease in the contribution of each electrode to a distant current field is realized by electrically insulating the electrodes from any contiguous tissue other than the muscle to be stimulated, with this insulation being accomplished by the placing of an insulating material between the attached electrodes and the contiguous structures.
  • Further current field localization can be realized by electrically isolating the electrode poles so that no current can flow between them.
  • Apparatus for stimulating a mass of electrically excitable tissue comprising:
  • pulsegenerating means for providing predetermined timed sequences of electrical pulses, said pulse-generating means including tuned circuit means for responding to radiofrequency signals for providing power signals; rectifier and filter means coupled to said tuned circuit means for providing direct current signals in response to said power signals; and
  • control means coupled intermediate said plurality of electrodes and said pulse-generating means for controlling the time and sequence of application of said electrical pulses to individual ones of said electrode means, said control means including clocking means for controlling said time and sequence of application of said electrical pulses to only one of said electrode means at any given time, and including pulse circuit means coupled to said rectifier and filter means for generating pulses in response to said direct current signals, a plurality of insulated electrical conductors electrically coupled intermediate said pulse circuit means and said plurality of electrically conductive electrode means for transmitting said pulses to said electrode means; said clocking means coupled to said pulse circuit means for controlling the sequence of said transmitting of said pulses to individual ones of said plurality of electrically conductive electrode means in a predetermined order.
  • Apparatus for stimulating a mass of electrically excitable tissue comprising:
  • pulse-generating means for providing predetennined timed sequences of electrical pulses, said pulse generating means including a like plurality of power source means for generating sequences of signals, and a like plurality of pulse-generating means, each of said pulse-generating means electrically coupled to a respectively associated one of said plurality of power source means for providing said pulses to an associated one of said plurality of electrodes;
  • control means coupled intermediate said plurality of electrodes andsaid pulse-generating means for controlling the time and sequence of application of said electrical pulses to individual ones of said electrode means, said control means including clock circuit means coupled to said plurality of pulse-generating means for controlling said time and sequence of application of said pulses to only one of said electrode means at any given time, said clock circuit means including means for isolating each of said electrode means from the others of said electrode means.
  • each of said electrode means includes a pair of electrically conductive wires, a first plurality of electrical interconnection elements electrically coupled to one of said pair of conductive wires, and a second plurality of electrical interconnection elements electrically coupled to the other of said pair of conductive wires, and insulation means for insulating said pair of electrically conductive wires while leaving said first and second pluralities of interconnection elements exposed.
  • Apparatus for stimulating a mass of electrically excitable tissue comprising:
  • pulsegenerating means for providing predetermined timed sequences of electrical pulses, said pulse-generat- 5 ing means includingtuned circuit means for responding to high-frequency signals for providing power signals; rectifier and filter means coupled to said tuned circuit means for providing direct current signals in response to said power signals; and v c. control means coupled intermediate said plurality of elec- 3. suturing with electrically conductive wire each of the electrical interconnection points to predetermined depths in the tissue to be stimulated for electrically coupling to the neural system innervating the tissue to be stimulated; and
  • said control means including clocking means for controlling said time and'sequence of application of said electrical pulses to only one of said electrode means at any given time, and including pulse circuit means coupled to said rectifier and filter means for generating pulses in response source and those portions of the electrodes other than said predetermined points of contact for further minimizing undesired stimulation of contiguous tissue structures.
  • a bipolar electrode for use with an implantable stimulator for stimulating electrically excitable tissue comprising:
  • the method of stimulating a mass of electrically excitable tissue while preventing undesired stimulation of contiguous tissue structures comprising the steps of:
  • insulation means for insulating said pair of electrically

Abstract

An apparatus for implantation in the body to locally stimulate a mass of electrically excitable tissue without stimulating nearby tissue structures, and the method of so stimulating the tissue is described. The apparatus includes a plurality of electrodes, each of the electrodes including a pair of conductors for carrying signals of positive and negative polarity, each of said conductors having a plurality of electrically conductive coupling points for coupling to the mass of tissue. Apparatus is also described for providing timed sequenced electrical impulses to the plurality of electrodes so that only one of the electrodes has a voltage applied between its input terminals at any given time. An insulating backing placed between the electrodes and tissue structures surrounding the implanted stimulator for eliminating undesirable secondary tissue stimulation is also described. The method of applying controlled time-spaced electrical impulses to a mass of electrically excitable tissue structure for causing stimulation of that tissue structure is also described.

Description

United States Patent Timm et al.
[ Mar. 7, 1972 [54] IMPLANTABLE ELECTRONIC STIMULATOR ELECTRODE AND FOREIGN PATENTS OR APPLICATIONS 130,797 l/l969 Czechoslovakia ..l28/4l8 METHOD 72 l t Gerald w. T'mm' William E. Bradle Emmi'ler-"william (3mm 1 men ors both of Minnegpolis Minn. Attorney-Burd, Braddock & Bartz [73] Assignee: The Regents of the University of Min- 1 57 S T nesota, Minneapolis, Minn. An apparatus for implantation in the body to locally stimulate Filed: y 15, 1969 a mass of electrically excitable tissue without stimulating near- [21] Appl' 841,756 by tissue structures, and the method of so stimulating the tissue is described. The apparatus includes a plurality of electrodes, each of the electrodes including a pair of conductors [52] US. Cl ..l28/42l, 128/418 f carrying i l f positive and negative polarity, each f [51] Int. Cl. ..A6ln l/36 Said Conductors having a plurality pf electrically conductive [58] Field 01' Search ..128/404, 410, 41 1, 416, 418 P, coupling points for coupling to the m of tissue Apparatus is 128/419 422 also described for providing timed sequenced electrical impulses to the plurality of electrodes so that only one of the elec- [56] References cued trodes has a voltage applied between its input terminals at any UNITED STATES PATENTS given time. An insulating backing placed between the electrodes and tissue structures surrounding the implanted stimul,597,061 8/1926 Cultra 128/404 lator for eliminating undesirable secondary tissue stimulation 2,065,295 12/1936 Sullivan 128/418 is also described. The method of applying controlled time- 2,338,672 6/1958 Faust Mus/422 spaced electrical impulses to a mass of electrically excitable 3,195,540 7/ 1965 Waller tissue structure for causing stimulation of that tissue structure 3,236,240 2/1966 Bradley ..128/42l is also described 3,279,468 10/1966 Levine .128/419 R 3,405,715 10/1968 Hagfors 128/418 9 Claims, 9 Drawing Figures V GEN. l 74 4 I2 56 P52 PULSE 1321:6112 v2 V GEN. 2 7e 2 g 68 z 2 PSn l l PULSE Vn GEN. n mil-I! O O O l I 78 72 fi' gfl ISOLATION CIRCUITS PAIENTEnm 11972 SHEET 1 OF 2 n M m S A R m mm Wm m M M M L M w s m E 2 m T ATTORNEYS IMPLANTABLE ELECTRONIC STIMULATOR ELECTRODE AND METHOD The invention described herein was made in the course of work under a grant or award from the Department of Health, Education and Welfare.
BACKGROUND OF THE INVENTION 1. Field of the Invention This invention relates to apparatus and method for artificially and electrically stimulating masses of electrically excitable tissue. More specifically, this invention relates to an apparatus and method for electrically stimulating tissue in those persons who have lost the voluntary neural control of this excitable mass because of injury or disease, such as for example, loss of bladder function due to spinal cord injury.
2. Description of the Prior Art Certain systems for artificially stimulating muscle activity are known to the prior art. One of the systems developed in the prior art is described in U.S. Pat. No. 3,236,240. The apparatus therein disclosed utilized spaced-apart electrodes to stimulate large areas of the bladder smooth muscle with volitionally generated electrical signals. It has been found that stimulation of such large areas usually results in stray electrical signals causing stimulation of nearby muscles and excitable tissue, an undesired secondary effect. In some instances, it has been determined that the stimulating signals cause a dual effect, the bladder muscle attempts to contract, as desired for evacuation thereof, but also the contraction of the external urethral sphincter takes place thereby inhibiting the evacuation of fluid from the bladder. Previous methods and apparatus of stimulating large tissue masses exhibit a disadvantage in that additive fields in the vicinity of the stimulated muscle can still occur owing to the parallel connection of multiple electrodes. That is, by the simultaneous application of a plurality of electrical fields resulting from the application of equal voltages to each of the electrodes, there will be generated at various points in the stimulated muscle, electrical fields that are greater than the individual fields resulting from each of the electrodes. Since the surrounding muscle tissue of concern often contains rapidly accommodating nerve fibers with low stimulus thresholds, these increases in field strength can be sufiicient to cause undesired muscle fiber stimulation.
SUMMARY ln summary, then, this invention comprises a method and apparatus for locally stimulating masses of electrically excitable tissue in the presence of other excitable physiologic structures. Unless specific limitation is set forth, muscle will often be used generically to cover all masses of electrically excitable tissue structures. The apparatus developed includes circuitry for providing nonsimultaneous or sequentially timed electrical impulses to various portions of the excitable mass. A plurality of electrodes are electrically coupled to the mass, for instance the detrusor muscle of a urinary bladder, for providing electrical stimulation to the neural conducting system innervating the muscle in response to the application of electrical energy to individual ones of the electrodes. Clocking and gating circuits are used for controlling the time and sequence of application of electrical impulses to the electrodes in a manner such that only one electrode is energized at any given time. In order to maximize the effectiveness of the nonsimultaneous or sequentially timed electrical impulses, specially formed electrodes are utilized. These electrodes are bipolar in construction and are arranged to have a plurality of electrically conductive connection points for coupling to the muscle at a plurality of positions. Insulation is provided for electrically isolating the electrodes from contiguous muscle structures that might receive undesired stimulations.
Urinary sepsis secondary to neurogenic dysfunction associated with spinal cord trauma, has been recognized as a clinical problem. Further, it has been recognized that prolonged use of indwelling catheters in paraplegic patients produces significant bacteriuria, cystitis, vesical calculi, and
pyelonephritis. Bladder tonus, or the response of the bladder smooth muscle to the stretch imposed by filling, has been described as anintrinsic property of smooth muscle and not reflex in nature. Changes in this response are shown to follow physical alteration in the bladder tissue. Regular, complete evacuation of the neurogenic bladder with avoidance of inflection and damage, is therefore an aid in preserving normal tonus and facilitating rehabilitation of bladder function. Electrical excitability of the mammalian bladder has been demonstrated. Further, various forms of implantable muscle or bladder stimulators have been described, as indicated by U.S. Pat. No. 3,236,240.
It is a primary object of this invention to provide a method and apparatus for providing electrode means, delivering electrical impulses to the electrode means extending over an adequate mass and at a sufficient depth in the mass of excitable tissue to activate the neural conduction system innervating the mass. Yet another object of this invention is to provide apparatus including electrode means, circuitry for providing nonsimultaneous electrical impulses to the electrode means electrically coupled to various portions of an excitable tissue structure. Still another object of this invention is to provide an implantable stimulator that utilizes a plurality of electrodes with the electrode being electrically coupled to the excitable tissue structure, for instance the detrusor muscle of the urinary bladder, for providing electrical stimulation to the neural conducting system innervating the structure, in response to the application of timed electrical energy impulses. Still another object of this invention, is to provide an implantable muscle stimulator apparatus having electrode means with circuitry including clocking and gating circuits being utilized for controlling the time and sequence of application of electrical impulses to a plurality of such electrodes in a manner such that only one electrode is energized at any given time. Still another object of this invention is to provide a practical method and means for artificially and electrically stimulating the bladder muscle to permit regular, complete evacuation, with the avoidance of infection and tissue damage. It is a further object of this invention to provide an implantable internal bladder stimulator in the form of electrodes coupled to a radio frequency receiver with the electrodes attached at a plurality of points to the bladder muscle, capable of providing properly timed stimuli of the bladder muscle when used in conjunction with an external radiofrequency transmitter. Still another object of this invention is to provide a passive internal bladder muscle stimulator adapted to be implanted subcutaneously and being provided with electrodes which are electrically attached to the bladder muscle, wherein the stimulator derives its properly timed stimulation power for each of the electrodes from an external high-power radiofrequency transmitter. Yet a further object of this invention is to provide an implantable muscle stimulator that is so operated in a nonsimultaneous manner of activation of a plurality of electrodes, and is so insulated, that contiguous tissue structures to which the electrodes are coupled are not stimulated. Also, the stimulator provides nonsimultaneous impulses to a plurality of electrodes by way of output circuits electrically isolated and arranged so that current flow between the output circuits is prevented thereby preventing the generation of massive current fields between the electrodes. The foregoing and other more detailed and specific objectives will become apparent from the following detailed description of the invention setting forth in detail certain illustrative embodiments of the invention, these being indicative, however, of but a few of the various ways in which the principle of the invention may be employed.
BRIEF DESCRIPTION OF THE DRAWINGS The invention will be described with reference to the drawings in which:
FIG. 1 is a perspective view of an internal implantable stimulator according to the present invention;
FIG. 2 illustrates the timed sequential application of electrical pulses to individual stimulator electrodes when, for example, n=3, or three output circuits are utilized;
FIG. 3 illustrates a type of bipolar electrode design utilizing two coils of conductor and having a plurality of electrical interconnection points;
FIG. 4 illustrates a characteristic placement of electrodes on a urinary bladder, with two electrodes near the lateral ligaments on the ventral surface and one electrode on the caudalrostral midline of the dorsal surface;
FIG. 5 illustrates a method of electrically connecting an electrode into the depth of a muscle structure, and illustrates the insulating backing for providing electrical isolation of stimuli from contiguous excitable structures surrounding a muscle;
FIG. 6 is a schematic block circuit diagram of an implantable muscle stimulator deriving its stimulation power from an external power transmitter, and having clocking and pulse circuits for applying electrical impulses to only one electrode at a time;
FIG. 7 is an alternative embodiment of the invention, and is a schematic block circuit diagram of an implantable muscle stimulator utilizing a separate power source and pulse circuit for each bipolar electrode with isolating clock circuitry for determining the pulse application sequence so that only one electrode is energized at any instant of time;
FIG. 8 is a plot of a characteristic muscle pressure response derived from the simultaneous application of a plurality of electrical impulses; and
FIG. 9 is a characteristic plot of pressure response obtained from a muscle having a plurality of electrical impulses sequentially applied.
DESCRIPTION OF THE PREFERRED EMBODIMENT As shown in FIG. 1, the implantable stimulator comprises a receiver, indicated generally at 10, and a plurality of bipolar electrodes 11 for attachment to the muscle. The electrodes 11 are connected to the receiver 10 by electrical conductors 12. The receiver I0 is encased in a protective mass 13, preferably sterilizable, inert, nonirritating and nontoxic protective material, for example composed of a synthetic resinous material. The conductors 12 are similarly encased in protective sheets 14, shown foreshortened to expose the conductive wires 12. The electrodes 11 are bipolar and receive voltage signals VI through Vn respectively. Each of the electrodes 11 is adapted for coupling to a pair of lines 12, with one of the lines 12 being designated and others of the line 12 being designated As summarized above, the invention embodies a method and apparatus for applying electrical stimuli to large masses of excitable muscle tissue without current spread to excitable tissue contiguous to the muscle to be stimulated. The stimuli are applied through the multiple bipolar electrodes 11 with the two poles of each electrode being electrically isolated from any of the poles of the other electrodes. In addition, the stimuli are developed in a manner whereby only one electrode has a voltage applied between its poles at any given time. In this regard, attention is directed to FIG. 2. There it can be seen that voltage pulses are applied to the bipolar electrodes in a nonsimultaneous or ordered manner so that additive stimulus fields are prevented. In FIG. 2, voltage along the vertical axis is plotted versus time along the horizontal axis, with the time being expressed in groupings of milliseconds.
While it is intended that the implantable stimulator 10 will be utilized with various kinds of muscles, specific examples of pulsing rates have been developed for the detrusor muscle of a urinary bladder. In this regard, experiments show effective stimulus application rates for bladder muscles is between approximately IO and 40 pulses per second with pulse durations between 0.5 and 5 milliseconds at each bipolar electrode 11, with voltage amplitude of up to about 50 volts.-Stimulus rates up to 120 pulses per second with durations as short as 0.1 millisecond are found to be effective for intestine and other muscle stimulation. Of course it is readily apparent that different times and rates of pulse occurrence and sequencing for the turning on and off of pulses to the electrodes 11 are contemplated by this invention, when certain contractile sequences of acceptable tissue are desired. It should further be understood that the manner of coupling the electrodes 11 to the muscle structure is important, and that other durations d and different pulse spacings p will be required to achieve the desired contractile operation.
To facilitate the proper electrical coupling to the muscle, the electrode shown in FIG. 3 was developed. The bipolar electrode is referred to generally as 11, with the leads being designated 12+ and 12. It has been determined electrode 11 of this design is especially efficient for providing a stimulus current over an adequate mass and at a sufiicient depth in the detrusor muscle to activate the neural conduction system innervating it. The conductors 12+ and 12- are fashioned from flexible coils or wires of Platinum-Iridium (Pt-Ir) wire or other suitable implantable conductor such as carbon-impregnated cloth, etc. The conductors 12+ and 12- may be constructed from other metals such as tantalum, gold, silver, and alloys of these metals with other metals. As stated above, the receiver 10 components are encased or embedded in a sterilizable, inert, nonirritating and nontoxic protective insulating mass 13, preferably of a synthetic resinous material, with only the conductors 12 leading to the muscle stimulating electrodes 1 1 extending therefrom. These conductors 12 are insulated by encasing them in a similar synthetic resinous protective and insulating material, or by coating them with a similar substance. Substances which operate both for the stimulator l0 and the wires 12, with the desired insulating characteristics, are silicone rubber, silastic resins, tetrafiuoroethylene polymers, vinyl chloride and the like, and are suitable materials for these purposes. Pure natural rubber may also be used. A first plurality of conductive tabs 16 may be electrically connected to the wire 12+, and a second plurality of tabs 18 may be electrically coupled to wire 12- for ease of connection. Each of the tabs contains an aperture for use in fastening the electrode 11 to the muscle. This will be described in more detail below. These tabs 16 and 18 are constructed of the same material as the conductors 12+ and l2. The distances D1 and D2 can be varied and adjusted to accommodate different muscle sizes. It should be noted also that greater or fewer numbers of tabs 16 and 18 can be utilized both in parallel or in series with the conductors 12+ and 12. Further, for any particular muscle stimulation, the number of tabs and electrical interconnections may vary among the various electrodes 11. It will be appreciated, of course, that a variety of electrode configurations may be successfully employed in connection with the present invention. For example, in lieu of the conductive tabs referred to hereinabove, various areas of electrical insulation may be bared from the conductor surface, and the electrodes effectively coupled to the tissue in this fashion. Also, in FIG. 3 of the drawings, a single electrode is illustrated, and it will be appreciated that two, three, or more electrodes may be utilized, and may be energized in sequential order, or may be energized as multiple pairs. In some instances, it may be desirable to utilize relatively large grid patterns which include a substantial number of individual electrode elements.
A characteristic placement when three electrodes 11 are used is illustrated in FIG. 4 on a bladder 20. In this arrangement, the electrode 11 supplied with energy source V1 is applied at the caudal-rostral midline of the dorsal surface, shown in dashed line, and the two electrodes 1 1 energized by sources V2 and V3, are placed near the lateral ligaments on the ventral surface. In this arrangement, it is noted that the number of attachment points can be varied to accommodate different sized bladders 20. In the configuration shown, the ventral electrodes each utilize six tabs, whereas the single dorsal electrode utilizes eight tabs. For this arrangement, bladders of approximately ISO to 300 cc. capacities can be accommodated. Additional electrodes 11 may also be added to stimulate larger bladders.
In FIG. 5 there is shown a sectional view of a portion of the bladder muscle 20, together with a portion of an electrode 1 I. Only the 12+ wire together with the 14+ insulation is shown. in this arrangement, there are three tabs 16, each having wires or thread 22 sewn through the apertures therein and for a predetermined depth into the muscle. In this arrangement, the wires 22 are metal sutures, and are inserted approximately 2 to 3 millimeters into the bladder wall and tied to the holes in tabs 16. This arrangement provides for electrical contact from the conductor 12+ into the detrusor muscle. The electrodes 11 so designed and attached were made of a flexible design to follow the contour of the bladder during micturition. The wires 22 can be of the same material as the electrode wires 12+ and l2, or other suitable electrically conductive materials. Once the electrodes are sutured to the muscle, a thin sheet of insulating material, for instance, silastic, is placed over the electrodes to prevent stimulation of contiguous excitable structures. In FIG. 5, this insulation is represented in cross section as element 24, and characteristically, can be in the order of 0.005 inch in thickness.
Having considered the general operational system, and the application of electrodes to the muscles, attention will next be directed to FIG. 6 wherein there is shown a schematic block circuit diagram of an implantable muscle stimulator deriving its stimulation power from an external transmitter. The portion of the stimulator shown enclosed within dashed block 30 includes a tuned resonant circuit 32, which characteristically can be comprised of an inductor and a capacitor in a parallel-connected resonant circuit. Such a circuit has the ability to store energy for short periods of time and tends to act as an energy reservoir. Further, the inductor of the tuned circuit 32 acts as an antenna, for picking up pulses of radiofrequency energy from an external highpower transmitter of conventional design (not shown), where such energy is transmitted through layers of body tissue to the tuned circuit 32. The tuned circuit 32 is coupled to a circuit identified as rectifiers and filters 34 as indicated by arrow 36. The signals provided by the tuned resonant circuit 32 are rectified into DC signals by filtering out the radiofrequency and the DC voltage so developed is applied at the output of the rectifiers and filters 34. In this invention, the signals are directed on lines 38 to clocking and pulse circuits 40 wherein the signals applied from lines 38 are converted to pulses and are alternatively applied to lines 42, 44, and 46 in substantially nonsimultaneous order. The signals provided on lines 38 are converted to pulses by means of pulse generators, or multivibrators, of types available commercially, and these pulses are applied to the bipolar electrodes 42, 44, and 46 for durations determined by the clocking circuitry. The clocking circuitry can be selected from various types of circuit components and arrangements well known in the prior art. Isolation elements 11, labeled 48; I2 labeled 50; and In labeled 52, are provided for isolating the electrodes electrically. Such isolation between electrodes can be provided for example by isolation transformers, or by simple diode arrangements for performing isolation as is well known. The signals provided from the isolation elements are taken directly to the electrodes with the wires being indicated by reference numeral 12, as previously used. It can be seen that the function of the clocking and pulse circuits 40 is to provide a planned application of signals to the isolation elements 48, 50, and 52 in a manner similar to that illustrated in FIG. 2. Only one of the bipolar lines 12 will carry signals at any given time.
An alternative embodiment is illustrated in FIG 7, wherein there is shown in schematic block diagram form an alternative implantable muscle stimulator 10. In this arrangement, a plurality of power sources indicated as PS1 labeled 54; PS2 labeled 56; and PSn labeled 58, is utilized, with a separate one of the power sources used for each of the bipolar electrodes 11. In this arrangement, there is utilized a plurality of pulse generators, with pulse generator 1, labeled 60, being coupled by line 62 to power source PSI. In a similar manner, pulse generator 2, labeled 64, is coupled by lines 66 to power source PS2. Finally, pulse generator n, labeled 68, is coupled by lines 70 to PSn. The output signals from the pulse generators 60, 64 and 68 are controlled by the clock circuit 72 respectively. A clock circuit 72 can be any well-known isolating clock circuitry, such as ring counters, or the like, used to determine the pulse enabling sequence to each of the electrodes. In this manner, the output line 74 from clock circuit 72 controls pulse generator 1, a signal on line 76 controls pulse generator 2,7 and the signal on line 78 controls pulse generator n. The output signals from the pulse generators 60, 64 and 68 are applied on lines 12 in a nonsimultaneous arrangement as described above. It is readily apparent that the duration of the pulses occurring on lines 74, 76 and 78 determine the duration d of the power pulses in conjunction of the availability of energy signals on lines 62, 66 and 70, respectively. It is further apparent, that the time duration between occurrences of signals on lines 74, 76 and 78 will determine the elapsed time between the activating pulses available on lines 12. Further, the duration of the count in clock circuit 72 until it completes the cycle will determine the duration d between consecutive signals on any given line V1, V2, and Vn.
In FIG. 8 there is illustrated on characteristic pressure response curve for the situation wherein a muscle is stimulated by the simultaneous occurrence of three electrical signals. Application thereby indicating that only partial voiding of the bladder has occurred. In this figure, M denotes micturition.
FIG. 9 illustrates a characteristic pressure response obtained in a bladder wherein pulses were applied nonsimultaneously through three electrodes as described above. In this operation, it can be seen that the intravesical pressure rise upon stimulus S application led to a more complete bladder evacuation as indicated by a drop in residual pressure following the termination of the application of the stimulus S. Again, M denotes micturition.
Experimentation with the evacuation of the urinary bladder leads to the conclusion that it is necessary to select the appropriate application of electrical stimuli to effect a detrusor contraction leading to sequential opening of the sphincters. Pressure increases leading to sphincter opening are achieved in an optimum fashion when the stimuli are nonsimultaneously applied via electrically isolated bipolar electrodes to the detrusor muscle, while limiting the current spread to surrounding excitable structures below their stimulus threshold. In a specific example of the simultaneous stimulation of three electrodes, as illustrated characteristically in FIG. 8, experimental results yielded an intravesical pressure rise to approximately 33 centimeters of water, but with only 20 cc. of a 200 cc. bladder being voided. In the experimental operation, there was no visible sign of current field spread observed, but due to the poor voiding response, it is believed that there was current spread to the pudendal nerve, thereby forcing the external sphincter to contract. Further experimentation with the application of sequential stimulating pulses, with a characteristic response curve shown in FIG. 9, demonstrated that there was a sharp intravesical pressure increase followed by rapid evacuation of the entire capacity of the 200 cc. bladder with no sign of stimulus spread. In FIG. 9, the sharp peaks in the pressure response curve correspond to the pulsatile contractions of the bladder and forceful streams from the urethra.
As indicated above, evacuation of the urinary bladder requires appropriate application of the electrical stimuli to effect a detrusor contraction, leading to sequential opening of the sphincters. It has been determined that these contractile responses are obtained when pulses are applied at a rate of approximately l0-40 per second with durations of approximately 0.5 to 5 milliseconds and amplitudes up to about 50 volts. The foregoing mentioned experiments were conducted by applying bipolar pulses of l-millisecond duration at a rate of 20 per second with an approximate amplitude of 30 volts.
Since relatively large current fields are generated when stimulating the detrusor muscle, a combination of insulating the electrodes from the contiguous muscle structures, together with the nonsimultaneous application of energizing signals to the electrodes from electrically isolated outputs has been employed to restrict the spread of current fields to excitable structures surrounding the bladder. The nonsimultaneous application of pulses to the electrodes attached to the muscle causes less spread than simultaneous application of pulses thereto. This can clearly be understood by considering that the stimuli applied to each electrode are electrically independent and electrically isolated from one another. If a point in the muscle equidistant from the three electrodes is considered, the field generated at this point by each electrode is identical if the electrodes are the same and equal voltages are applied to them. Consequently; the application of pulses to the electrodes simultaneously results in a field at this point of approximately triple intensity, where three electrodes are used, while nonsimultaneous application gives a single field intensity occurring three times as often. Since the surrounding tissue of concern contains rapidly accommodating nerve fibers with low stimulus thresholds, the increase in frequency of stimulus application to these fibers does not greatly afiect their function, but the lower current at this point helps the field of strength to remain below simulus thresholds of the nerve fibers. If a point nonequidistant from the electrodes is considered, the contribution of each electrode to the current field will be different and the total field somewhat less than that described above. Sequencing results in decreases in the field at the point, with this decrease being realized when changing from simultaneous to nonsimultaneous stimulus application. A further decrease in the contribution of each electrode to a distant current field is realized by electrically insulating the electrodes from any contiguous tissue other than the muscle to be stimulated, with this insulation being accomplished by the placing of an insulating material between the attached electrodes and the contiguous structures. Further current field localization can be realized by electrically isolating the electrode poles so that no current can flow between them.
From the foregoing, it is clear that the various stated objectives and purposes of the invention have been achieved by the apparatus and method described. it is recognized that various alternations in dimensions, circuit component selections, tolerances, and timing, and the like, will become apparent to those skilled in the art without departing from the spirit and scope of the invention. Accordingly, what is intended to be protected by Letters Patent is set forth in the appended claims.
We claim:
1. Apparatus for stimulating a mass of electrically excitable tissue comprising:
a. a plurality of electrically conductive electrode means for electrically coupling to a mass of electrically excitable tissue, said electrode means including a pair of electrically conductive wires, a first plurality of electrical interconnection elements electrically coupled to one of said pair of conductive wires, and a second plurality of electrical interconnection elements electrically coupled to the other of said pair of conductive wires, electrically conductive connection means for electrically interconnecting each of said interconnection elements with predetermined portions of the tissue to be stimulated, insulation means for insulating said pair of electrically conductive wires while leaving said first and second pluralities of interconnection elements exposed, and isolation means coupled to said plurality of conductors for electrically isolating each of said electrode means from the others of said electrode means;
b. pulsegenerating means for providing predetermined timed sequences of electrical pulses, said pulse-generating means including tuned circuit means for responding to radiofrequency signals for providing power signals; rectifier and filter means coupled to said tuned circuit means for providing direct current signals in response to said power signals; and
c. control means coupled intermediate said plurality of electrodes and said pulse-generating means for controlling the time and sequence of application of said electrical pulses to individual ones of said electrode means, said control means including clocking means for controlling said time and sequence of application of said electrical pulses to only one of said electrode means at any given time, and including pulse circuit means coupled to said rectifier and filter means for generating pulses in response to said direct current signals, a plurality of insulated electrical conductors electrically coupled intermediate said pulse circuit means and said plurality of electrically conductive electrode means for transmitting said pulses to said electrode means; said clocking means coupled to said pulse circuit means for controlling the sequence of said transmitting of said pulses to individual ones of said plurality of electrically conductive electrode means in a predetermined order.
2. Apparatus as in claim 1 and further including further insulation means for electrically insulating said plurality of electrode means from contiguous stimulatable tissue structures for inhibiting undesired stimulation thereof.
3. Apparatus for stimulating a mass of electrically excitable tissue comprising:
a. a plurality of electrically conductive electrode means for electrically coupling to a mass of electrically excitable tissue:
b. pulse-generating means for providing predetennined timed sequences of electrical pulses, said pulse generating means including a like plurality of power source means for generating sequences of signals, and a like plurality of pulse-generating means, each of said pulse-generating means electrically coupled to a respectively associated one of said plurality of power source means for providing said pulses to an associated one of said plurality of electrodes; and
c. control means coupled intermediate said plurality of electrodes andsaid pulse-generating means for controlling the time and sequence of application of said electrical pulses to individual ones of said electrode means, said control means including clock circuit means coupled to said plurality of pulse-generating means for controlling said time and sequence of application of said pulses to only one of said electrode means at any given time, said clock circuit means including means for isolating each of said electrode means from the others of said electrode means.
4. Apparatus as in claim 3 wherein each of said electrode means includes a pair of electrically conductive wires, a first plurality of electrical interconnection elements electrically coupled to one of said pair of conductive wires, and a second plurality of electrical interconnection elements electrically coupled to the other of said pair of conductive wires, and insulation means for insulating said pair of electrically conductive wires while leaving said first and second pluralities of interconnection elements exposed.
5. Apparatus as in claim 4 and further including electrically conductive connection means for electrically interconnecting each of said interconnection elements with predetermined portions of the tissue to be stimulated.
6. Apparatus for stimulating a mass of electrically excitable tissue comprising:
a. a plurality of electrically conductive electrode means for electrically coupling to a mass of electrically excitable tissue, said electrode means including a pair of electrically conductive wires, a first plurality of electrical interconnection elements electrically coupled to one of said pair of conductive wires, and a second plurality of electrical interconnection elements electrically coupled to the other of said pair of conductive wires, electrically conductive connection means for electrically interconnecting each of said interconnection elements with predetermined portions of the tissue to be stimulated, insulation means for insulating said pair of electrically conductive wires while leaving said first and second pluralities of interconnection elements exposed, and isolation means 3 ,646,940 ,9 10 coupled to said plurality of conductors for electrically isolating each of said electrode means from the others of said electrode means;
b. pulsegenerating means for providing predetermined timed sequences of electrical pulses, said pulse-generat- 5 ing means includingtuned circuit means for responding to high-frequency signals for providing power signals; rectifier and filter means coupled to said tuned circuit means for providing direct current signals in response to said power signals; and v c. control means coupled intermediate said plurality of elec- 3. suturing with electrically conductive wire each of the electrical interconnection points to predetermined depths in the tissue to be stimulated for electrically coupling to the neural system innervating the tissue to be stimulated; and
b. generating pulses with a pulse source and applying the generated pulses to one electrode at a time in a predetermined sequence.
8. The method of claim 7 and further including the steps of:
a a. implanting a controlled pulse source in the body; and
b. placing an insulating cover over the implanted pulse trodes and said pulse-generating means for controlling the time and sequence of application of said electrical pulses to individual ones of said electrode means, said control means including clocking means for controlling said time and'sequence of application of said electrical pulses to only one of said electrode means at any given time, and including pulse circuit means coupled to said rectifier and filter means for generating pulses in response source and those portions of the electrodes other than said predetermined points of contact for further minimizing undesired stimulation of contiguous tissue structures.
9. A bipolar electrode for use with an implantable stimulator for stimulating electrically excitable tissue comprising:
a. a pair of electrically conductive wires for receiving bipolar pulses, one of said pair of electrically conductive wires being arranged in a predetermined serpentine patto said direct current signals, a plurality of insulated electefn, the other of said P electrically cQnductive trical conductors electrically coupled intermediate said wlfes being P E sulimamlally a mlrfol Image 9 pulse circuit means and said plurality of electrically con- 531d py =q serpentme Pattern and Overlap-S ductive electrode means for transmitting said pulses to one at {P i p i said electrode means; said clocking means coupled to said a first Plumhty P spacedrapafl electrical "ftefcQnnecllon pu|se circuit means f controlling the Sequence f said elements electrically coupled to one of said pair of contransmitting of said pulses to individual ones of said plurality of electrically conductive electrode means.
ductive wires; a second plurality of spaced-apart electrical interconnection elements electrically coupled to the other of said pair of conductive wires; with individual ones of said first and second pluralities of interconnection elements paired and positioned at approximately the midpoints between associated ones of said plurality of over- 7. The method of stimulating a mass of electrically excitable tissue while preventing undesired stimulation of contiguous tissue structures comprising the steps of:
a. electrically affixing a set of spaced-apart electrodes to the mass of tissue to be stimulated, said step of affixing including the steps of:
1. providing a plurality of electrical interconnection points on each of the electrodes;
2. selecting predetermined points of contact; and
lap points; and
. insulation means for insulating said pair of electrically

Claims (11)

1. Apparatus for stimulating a mass of electrically excitable tissue comprising: a. a plurality of electrically conductive electrode means for electrically coupling to a mass of electrically excitable tissue, said electrode means including a pair of electrically conductive wires, a first plurality of electrical interconnection elements electrically coupled to one of said pair of conductive wires, and a second plurality of electrical interconnection elements electrically coupled to the other of said pair of conductive wires, electrically conductive connection means for electrically interconnecting each of said interconnection elements with predetermined portions of the tissue to be stimulated, insulation means for insulating said pair of electrically conductive wires while leaving said first and second pluralities of interconnection elements exposed, and isolation means coupled to said plurality of conductors for electrically isolating each of said electrode means from the others of said electrode means; b. pulse-generating means for providing predetermined timed sequences of electrical pulses, said pulse-generating means including tuned circuit means for responding to radiofrequency signals for providing power signals; rectifier and filter means coupled to said tuned circuit means for providing direct current signals in response to said power signals; and c. control means coupled intermediate said plurality of electrodes and said pulse-generating means for controlling the time and sequence of application of said electrical pulsEs to individual ones of said electrode means, said control means including clocking means for controlling said time and sequence of application of said electrical pulses to only one of said electrode means at any given time, and including pulse circuit means coupled to said rectifier and filter means for generating pulses in response to said direct current signals, a plurality of insulated electrical conductors electrically coupled intermediate said pulse circuit means and said plurality of electrically conductive electrode means for transmitting said pulses to said electrode means; said clocking means coupled to said pulse circuit means for controlling the sequence of said transmitting of said pulses to individual ones of said plurality of electrically conductive electrode means in a predetermined order.
2. Apparatus as in claim 1 and further including further insulation means for electrically insulating said plurality of electrode means from contiguous stimulatable tissue structures for inhibiting undesired stimulation thereof.
2. selecting predetermined points of contact; and
3. suturing with electrically conductive wire each of the electrical interconnection points to predetermined depths in the tissue to be stimulated for electrically coupling to the neural system innervating the tissue to be stimulated; and b. generating pulses with a pulse source and applying the generated pulses to one electrode at a time in a predetermined sequence.
3. Apparatus for stimulating a mass of electrically excitable tissue comprising: a. a plurality of electrically conductive electrode means for electrically coupling to a mass of electrically excitable tissue: b. pulse-generating means for providing predetermined timed sequences of electrical pulses, said pulse generating means including a like plurality of power source means for generating sequences of signals, and a like plurality of pulse-generating means, each of said pulse-generating means electrically coupled to a respectively associated one of said plurality of power source means for providing said pulses to an associated one of said plurality of electrodes; and c. control means coupled intermediate said plurality of electrodes and said pulse-generating means for controlling the time and sequence of application of said electrical pulses to individual ones of said electrode means, said control means including clock circuit means coupled to said plurality of pulse-generating means for controlling said time and sequence of application of said pulses to only one of said electrode means at any given time, said clock circuit means including means for isolating each of said electrode means from the others of said electrode means.
4. Apparatus as in claim 3 wherein each of said electrode means includes a pair of electrically conductive wires, a first plurality of electrical interconnection elements electrically coupled to one of said pair of conductive wires, and a second plurality of electrical interconnection elements electrically coupled to the other of said pair of conductive wires, and insulation means for insulating said pair of electrically conductive wires while leaving said first and second pluralities of interconnection elements exposed.
5. Apparatus as in claim 4 and further including electrically conductive connection means for electrically interconnecting each of said interconnection elements with predetermined portions of the tissue to be stimulated.
6. Apparatus for stimulating a mass of electrically excitable tissue comprising: a. a plurality of electrically conductive electrode means for electrically coupling to a mass of electrically excitable tissue, said electrode means including a pair of electrically conductive wires, a first plurality of electrical interconnection elements electrically coupled to one of said pair of conductive wires, and a second plurality of electrical interconnection elements electrically coupled to the other of said pair of conductive wires, electrically conductive connection means for electrically interconnecting each of said interconnection elements with predetermined portions of the tissue to be stimulated, insulation means for insulating said pair of electrically conductive wires while leaving said first and second pluralities of interconnection elements exposed, and isolation means coupled to said plurality of conductors for electrically isoLating each of said electrode means from the others of said electrode means; b. pulse-generating means for providing predetermined timed sequences of electrical pulses, said pulse-generating means including tuned circuit means for responding to high-frequency signals for providing power signals; rectifier and filter means coupled to said tuned circuit means for providing direct current signals in response to said power signals; and c. control means coupled intermediate said plurality of electrodes and said pulse-generating means for controlling the time and sequence of application of said electrical pulses to individual ones of said electrode means, said control means including clocking means for controlling said time and sequence of application of said electrical pulses to only one of said electrode means at any given time, and including pulse circuit means coupled to said rectifier and filter means for generating pulses in response to said direct current signals, a plurality of insulated electrical conductors electrically coupled intermediate said pulse circuit means and said plurality of electrically conductive electrode means for transmitting said pulses to said electrode means; said clocking means coupled to said pulse circuit means for controlling the sequence of said transmitting of said pulses to individual ones of said plurality of electrically conductive electrode means.
7. The method of stimulating a mass of electrically excitable tissue while preventing undesired stimulation of contiguous tissue structures comprising the steps of: a. electrically affixing a set of spaced-apart electrodes to the mass of tissue to be stimulated, said step of affixing including the steps of:
8. The method of claim 7 and further including the steps of: a. implanting a controlled pulse source in the body; and b. placing an insulating cover over the implanted pulse source and those portions of the electrodes other than said predetermined points of contact for further minimizing undesired stimulation of contiguous tissue structures.
9. A bipolar electrode for use with an implantable stimulator for stimulating electrically excitable tissue comprising: a. a pair of electrically conductive wires for receiving bipolar pulses, one of said pair of electrically conductive wires being arranged in a predetermined serpentine pattern, and the other of said pair of electrically conductive wires being arranged in substantially a mirror image of said predetermined serpentine pattern and overlaps said one wire at a plurality of points; b. a first plurality of spaced-apart electrical interconnection elements electrically coupled to one of said pair of conductive wires; a second plurality of spaced-apart electrical interconnection elements electrically coupled to the other of said pair of conductive wires; with individual ones of said first and second pluralities of interconnection elements paired and positioned at approximately the midpoints between associated ones of said plurality of overlap points; and c. insulation means for insulating said pair of electrically conductive wires while leaving said first and second pluralities of interconnection elements exposed.
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Cited By (195)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3727616A (en) * 1971-06-15 1973-04-17 Gen Dynamics Corp Electronic system for the stimulation of biological systems
FR2196783A1 (en) * 1972-08-28 1974-03-22 Areca
US3851651A (en) * 1972-12-22 1974-12-03 P Icenbice Facial stimulating apparatus having sequentially energized electrodes
US3888261A (en) * 1973-12-07 1975-06-10 Medtronic Inc Time shared stimulator
DE2457850A1 (en) * 1973-12-07 1975-06-12 Medtronic Inc CIRCUIT ARRANGEMENT FOR STIMULATING A BIOLOGICAL SYSTEM
US3893463A (en) * 1973-12-07 1975-07-08 Medtronic Inc Dual channel stimulator
US3945387A (en) * 1974-09-09 1976-03-23 General Electric Company Implantable cardiac pacer with characteristic controllable circuit and control device therefor
US3955560A (en) * 1974-06-10 1976-05-11 Stein Richard B Implantable neural electrode
FR2320762A1 (en) * 1975-08-11 1977-03-11 Medtronic Inc ELECTRICAL STIMULATION AND STIMULATOR DEVICE IMPLANTABLE IN A BODY
DE2742956A1 (en) * 1976-09-27 1978-03-30 Harry Henry Dr Leveen DEVICE FOR TREATMENT OF DISEASES IN ANIMALS WITH HIGH FREQUENCY RADIANT ENERGY
US4120306A (en) * 1976-01-22 1978-10-17 Vitatron Medical B.V. Cardiac pacer with pre-programmed power source interface means
US4157087A (en) * 1978-03-06 1979-06-05 Med General, Inc. Peripheral nerve stimulator
DE2811463A1 (en) * 1978-03-18 1979-09-20 Inst Kib Akademii Nauk Uk Ssr ELECTRIC STIMULATOR FOR HUMAN MUSCLES WITH BIOELECTRIC CONTROL
DE2926861A1 (en) * 1978-07-03 1980-01-24 Technion Res & Dev Foundation THROUGH THE SKIN-WORKING ARRANGEMENT TO REDUCE PAIN
DE2929293A1 (en) * 1979-07-11 1981-02-05 Sp Ni Ok Bjuro Marijskogo Resp DEVICE FOR ELECTRICALLY INFLUENCING MILK Glands
US4340063A (en) * 1980-01-02 1982-07-20 Empi, Inc. Stimulation device
US4431002A (en) * 1981-06-08 1984-02-14 Empi Inc. Modulated deep afferent stimulator
US4442839A (en) * 1981-04-27 1984-04-17 Empi, Inc. Method of modulating energy in train of electrical pulses
US4456012A (en) * 1982-02-22 1984-06-26 Medtronic, Inc. Iontophoretic and electrical tissue stimulation device
US4567900A (en) * 1984-06-04 1986-02-04 Moore J Paul Internal deployable defibrillator electrode
US4569351A (en) * 1984-12-20 1986-02-11 University Of Health Sciences/The Chicago Medical School Apparatus and method for stimulating micturition and certain muscles in paraplegic mammals
US4585005A (en) * 1984-04-06 1986-04-29 Regents Of University Of California Method and pacemaker for stimulating penile erection
US4592359A (en) * 1985-04-02 1986-06-03 The Board Of Trustees Of The Leland Stanford Junior University Multi-channel implantable neural stimulator
US4690146A (en) * 1985-06-17 1987-09-01 Chattanooga Corporation Neuromuscular stimulating apparatus
EP0234457A2 (en) * 1986-02-24 1987-09-02 Medtronic, Inc. Intramuscular lead
US4708145A (en) * 1982-06-01 1987-11-24 Medtronic, Inc. Sequential-pulse, multiple pathway defibrillation method
DK152609B (en) * 1979-07-04 1988-03-28 Sp Ni Ok Apparatus for electrical stimulation
US4763656A (en) * 1985-06-13 1988-08-16 Beatrice T. Kester Transcutaneous electrical nerve stimulation device and method
US4841973A (en) * 1987-09-21 1989-06-27 Stecker Harold D Electrical stimulators
US5105811A (en) * 1982-07-27 1992-04-21 Commonwealth Of Australia Cochlear prosthetic package
US5121754A (en) * 1990-08-21 1992-06-16 Medtronic, Inc. Lateral displacement percutaneously inserted epidural lead
US5193539A (en) * 1991-12-18 1993-03-16 Alfred E. Mann Foundation For Scientific Research Implantable microstimulator
US5193540A (en) * 1991-12-18 1993-03-16 Alfred E. Mann Foundation For Scientific Research Structure and method of manufacture of an implantable microstimulator
US5281219A (en) * 1990-11-23 1994-01-25 Medtronic, Inc. Multiple stimulation electrodes
US5291902A (en) * 1993-01-11 1994-03-08 Brent Carman Incontinence treatment
US5358514A (en) * 1991-12-18 1994-10-25 Alfred E. Mann Foundation For Scientific Research Implantable microdevice with self-attaching electrodes
US5425752A (en) * 1991-11-25 1995-06-20 Vu'nguyen; Dung D. Method of direct electrical myostimulation using acupuncture needles
US5447526A (en) * 1992-12-24 1995-09-05 Karsdon; Jeffrey Transcutaneous electric muscle/nerve controller/feedback unit
US5501703A (en) * 1994-01-24 1996-03-26 Medtronic, Inc. Multichannel apparatus for epidural spinal cord stimulator
US5524624A (en) * 1994-05-05 1996-06-11 Amei Technologies Inc. Apparatus and method for stimulating tissue growth with ultrasound
WO1998009679A1 (en) * 1996-09-05 1998-03-12 The Governors Of The University Of Alberta Gastro-intestinal electrical pacemaker
WO1998030280A1 (en) * 1997-01-13 1998-07-16 Medtronic, Inc. Apparatus and method for treating chronic constipation
US5833714A (en) * 1996-01-18 1998-11-10 Loeb; Gerald E. Cochlear electrode array employing tantalum metal
US5957958A (en) * 1997-01-15 1999-09-28 Advanced Bionics Corporation Implantable electrode arrays
WO2002009808A1 (en) 2000-07-26 2002-02-07 Advanced Bionics Corporation Rechargeable spinal cord stimulator system
US6381496B1 (en) 1999-10-01 2002-04-30 Advanced Bionics Corporation Parameter context switching for an implanted device
WO2002038217A3 (en) * 2000-11-09 2002-10-31 Neuropace Inc Implantable neuromuscular stimulator for the treatment of gastrointestinal disorders
US20020165589A1 (en) * 2001-05-01 2002-11-07 Imran Mir A. Gastric treatment and diagnosis device and method
US20020183817A1 (en) * 2000-12-07 2002-12-05 Paul Van Venrooij Directional brain stimulation and recording leads
US6516227B1 (en) 1999-07-27 2003-02-04 Advanced Bionics Corporation Rechargeable spinal cord stimulator system
US20030032992A1 (en) * 2001-08-13 2003-02-13 Thacker James R. System and method of rapid, Comfortable parameter switching in spinal cord stimulation
US6542776B1 (en) * 1999-04-14 2003-04-01 Transneuronix Inc. Gastric stimulator apparatus and method for installing
US20030078633A1 (en) * 2001-09-28 2003-04-24 Firlik Andrew D. Methods and implantable apparatus for electrical therapy
US20030093134A1 (en) * 2001-11-02 2003-05-15 Kerry Bradley Method for increasing the therapeutic ratio/usage range in a neurostimulator
US6606523B1 (en) * 1999-04-14 2003-08-12 Transneuronix Inc. Gastric stimulator apparatus and method for installing
US20030153959A1 (en) * 2002-02-12 2003-08-14 Thacker James R. Neural stimulation system providing auto adjustment of stimulus output as a function of sensed coupling efficiency
US20030191504A1 (en) * 1999-07-30 2003-10-09 Meadows Paul M. Implantable pulse generators using rechargeable zero-volt technology lithium-ion batteries
US20030195591A1 (en) * 1996-06-07 2003-10-16 Jay Law Multiprogrammable tissue stimulator and method
US6659968B1 (en) 2000-06-01 2003-12-09 Advanced Bionics Corporation Activity monitor for pain management efficacy measurement
US20030229387A1 (en) * 2000-02-08 2003-12-11 Medtronic, Inc. Surgical lead body
US6684104B2 (en) 1999-04-14 2004-01-27 Transneuronix, Inc. Gastric stimulator apparatus and method for installing
US6735474B1 (en) 1998-07-06 2004-05-11 Advanced Bionics Corporation Implantable stimulator system and method for treatment of incontinence and pain
US20040116978A1 (en) * 2002-12-06 2004-06-17 Kerry Bradley Method for determining stimulation parameters
US20040158170A1 (en) * 2003-02-04 2004-08-12 Overstreet Edward H. Method of rapid neural response measurement without amplitude attenuation
US20040260310A1 (en) * 2002-10-23 2004-12-23 Medtronic, Inc. Medical lead and method
US20050004622A1 (en) * 2003-07-03 2005-01-06 Advanced Neuromodulation Systems System and method for implantable pulse generator with multiple treatment protocols
US20050055063A1 (en) * 2001-07-20 2005-03-10 Loeb Gerald E. Method and apparatus for the treatment of urinary tract dysfunction
US6871099B1 (en) 2000-08-18 2005-03-22 Advanced Bionics Corporation Fully implantable microstimulator for spinal cord stimulation as a therapy for chronic pain
US20050090885A1 (en) * 2003-10-23 2005-04-28 Medtronic, Inc. Medical lead and manufacturing method therefor
US20050143784A1 (en) * 2001-05-01 2005-06-30 Imran Mir A. Gastrointestinal anchor with optimal surface area
US20050182470A1 (en) * 2002-10-23 2005-08-18 Medtronic, Inc. Paddle-style medical lead and method
US6941171B2 (en) 1998-07-06 2005-09-06 Advanced Bionics Corporation Implantable stimulator methods for treatment of incontinence and pain
US20050245987A1 (en) * 2002-02-04 2005-11-03 Woods Carla M Method for programming implantable device
US20050267546A1 (en) * 2004-05-28 2005-12-01 Jordi Parramon Low power loss current digital-to-analog converter used in an implantable pulse generator
US20060030918A1 (en) * 2004-08-04 2006-02-09 Chinn Kenny K Operating room lead connector
US7009313B1 (en) 2001-03-16 2006-03-07 Advanced Bionics Corporation Multi-compliance voltage generator in a multichannel current stimulator
US20060052782A1 (en) * 2004-06-07 2006-03-09 Chad Morgan Orthopaedic implant with sensors
US7020531B1 (en) 2001-05-01 2006-03-28 Intrapace, Inc. Gastric device and suction assisted method for implanting a device on a stomach wall
US20060070334A1 (en) * 2004-09-27 2006-04-06 Blue Hen, Llc Sidewall plank for constructing a trailer and associated trailer sidewall construction
US20060074457A1 (en) * 2001-05-01 2006-04-06 Imran Mir A Pseudounipolar lead for stimulating a digestive organ
US20060074458A1 (en) * 2001-05-01 2006-04-06 Imran Mir A Digestive organ retention device
US20060089699A1 (en) * 2001-05-01 2006-04-27 Imran Mir A Abdominally implanted stimulator and method
US20060111753A1 (en) * 2001-05-01 2006-05-25 Imran Mir A Gastric stimulation anchor and method
US7054689B1 (en) 2000-08-18 2006-05-30 Advanced Bionics Corporation Fully implantable neurostimulator for autonomic nerve fiber stimulation as a therapy for urinary and bowel dysfunction
US20060122653A1 (en) * 2001-12-04 2006-06-08 Kerry Bradley Apparatus and method for determining the relative position and orientation of neurostimulation leads
US20060173262A1 (en) * 2005-01-31 2006-08-03 Medtronic, Inc. Medical lead with segmented electrode
US7099718B1 (en) 2001-05-29 2006-08-29 Advanced Bionics Corporation Neural stimulation lead fixation
US20060195159A1 (en) * 2004-12-03 2006-08-31 Kerry Bradley System and method for choosing electrodes in an implanted stimulator device
US20060224222A1 (en) * 2005-04-01 2006-10-05 Kerry Bradley Apparatus and methods for detecting migration of neurostimulation leads
US7127298B1 (en) 2002-10-18 2006-10-24 Advanced Bionics Corporation Switched-matrix output for multi-channel implantable stimulator
US20060241722A1 (en) * 2005-04-26 2006-10-26 Thacker James R Evaluating stimulation therapies and patient satisfaction
US20060241721A1 (en) * 2005-04-26 2006-10-26 Sridhar Kothandaraman Display graphics for use in stimulation therapies
US7146223B1 (en) 2002-02-04 2006-12-05 Advanced Bionics Corporation Method for optimizing search for spinal cord stimulation parameter settings
US20060293723A1 (en) * 2003-12-19 2006-12-28 Whitehurst Todd K Skull-mounted electrical stimulation system and method for treating patients
US7162304B1 (en) 2003-05-08 2007-01-09 Advanced Bionics Corporation System for measuring cardiac rhythm parameters for assessment of spinal cord stimulation
WO2007008212A1 (en) 2005-07-08 2007-01-18 Advanced Bionics Corporation Current output architecture for an implantable stimulator device
US20070049991A1 (en) * 2005-08-30 2007-03-01 Klostermann Daniel J Telemetry-based wake up of an implantable medical device
US20070049990A1 (en) * 2005-08-30 2007-03-01 Klostermann Daniel J Telemetry protocol for ultra low error rates useable in implantable medical devices
US20070049986A1 (en) * 2005-09-01 2007-03-01 Imran Mir A Randomized stimulation of a gastrointestinal organ
US20070053466A1 (en) * 2005-09-08 2007-03-08 Klostermann Daniel J Frequency shift keying demodulation technique
US20070055308A1 (en) * 2005-09-06 2007-03-08 Haller Matthew I Ultracapacitor powered implantable pulse generator with dedicated power supply
US20070073354A1 (en) * 2005-09-26 2007-03-29 Knudson Mark B Neural blocking therapy
US20070083240A1 (en) * 2003-05-08 2007-04-12 Peterson David K L Methods and systems for applying stimulation and sensing one or more indicators of cardiac activity with an implantable stimulator
US20070100399A1 (en) * 2005-07-08 2007-05-03 Advanced Bionics Corporation Current Generation Architecture for an Implantable Stimulator Device Having Coarse and Fine Current Control
US20070135868A1 (en) * 2005-12-14 2007-06-14 Shi Jess W Techniques for sensing and adjusting a compliance voltage in an implantable stimulator device
WO2007067825A1 (en) 2005-12-07 2007-06-14 Advanced Bionics Corporation Battery protection and zero-volt battery recovery system for an implantable medical device
US7239920B1 (en) 2002-02-12 2007-07-03 Advanced Bionics Corporation Neural stimulation system providing auto adjustment of stimulus output as a function of sensed pressure changes
US20070156207A1 (en) * 2006-01-04 2007-07-05 Sridhar Kothandaraman Expanding single channel stimulator capability on multi-area stimulation programs
US20070239228A1 (en) * 2006-04-07 2007-10-11 Kerry Bradley System and method using multiple timing channels for electrode adjustement during set up of an implanted stimulator device
US20070260288A1 (en) * 2006-03-03 2007-11-08 Yossi Gross Apparatus for treating stress and urge incontinence
US7295878B1 (en) 1999-07-30 2007-11-13 Advanced Bionics Corporation Implantable devices using rechargeable zero-volt technology lithium-ion batteries
US20070265679A1 (en) * 2002-02-04 2007-11-15 Advanced Bionics Corporation Method for optimizing search for spinal cord stimulation parameter setting
US20070265675A1 (en) * 2006-05-09 2007-11-15 Ams Research Corporation Testing Efficacy of Therapeutic Mechanical or Electrical Nerve or Muscle Stimulation
US20070293914A1 (en) * 1999-07-27 2007-12-20 Advanced Bionics Corporation Patient programmer for implantable devices
US7317948B1 (en) 2002-02-12 2008-01-08 Boston Scientific Scimed, Inc. Neural stimulation system providing auto adjustment of stimulus output as a function of sensed impedance
US20080009914A1 (en) * 2006-07-10 2008-01-10 Ams Research Corporation Systems and Methods for Implanting Tissue Stimulation Electrodes in the Pelvic Region
US20080027500A1 (en) * 2006-07-28 2008-01-31 Advanced Bionics Corporation Charger With Orthogonal PCB For Implantable Medical Device
US20080058876A1 (en) * 2006-09-06 2008-03-06 Giancarlo Barolat Implantable reel for coiling an implantable elongated member
US20080065169A1 (en) * 2001-05-01 2008-03-13 Intrapace, Inc. Endoscopic Instrument for Engaging a Device
US20080071325A1 (en) * 2002-02-04 2008-03-20 Advanced Bionics Corporation Method for optimizing search for spinal cord stimulation parameter setting
US7363079B1 (en) 2002-09-26 2008-04-22 Boston Scientific Neuromodulation Corporation Power qualifier for electrical stimulation configurations
US20080103559A1 (en) * 2006-10-26 2008-05-01 Advanced Bionics Corporation Method of maintaining intensity output while adjusting pulse width or amplitude
US20080132970A1 (en) * 2006-12-05 2008-06-05 Giancarlo Barolat Method and system for treatment of intractable scrotal and/or testicular pain
US20080183224A1 (en) * 2007-01-25 2008-07-31 Giancarlo Barolat Electrode paddle for neurostimulation
US20080188909A1 (en) * 2007-02-01 2008-08-07 Boston Scientific Neuromodulation Corporation Neurostimulation system and method for measuring patient activity
US20080215119A1 (en) * 1999-01-07 2008-09-04 Boston Scientific Neuromodulation Corporation System and method for displaying stimulation field generated by electrode array
WO2008142402A1 (en) 2007-05-22 2008-11-27 Ivor Stephen Gillbe Array stimulator
US20090012592A1 (en) * 2006-07-10 2009-01-08 Ams Research Corporation Tissue anchor
US20090018606A1 (en) * 2005-10-12 2009-01-15 Intrapace, Inc. Methods and Devices for Stimulation of an Organ with the Use of a Transectionally Placed Guide Wire
US20090036946A1 (en) * 2001-11-29 2009-02-05 American Medical Systems, Inc. Pelvic disorder treatments
US7509175B2 (en) 2006-08-03 2009-03-24 Intrapace, Inc. Method and devices for stimulation of an organ with the use of a transectionally placed guide wire
US20090099439A1 (en) * 2007-10-16 2009-04-16 Giancarlo Barolat Surgically implantable electrodes
US20090112281A1 (en) * 2007-10-26 2009-04-30 Medtronic, Inc. Medical device configuration based on sensed brain signals
US20090157091A1 (en) * 2006-04-04 2009-06-18 Ams Research Corporation Apparatus for Implanting Neural Stimulation Leads
US7603179B1 (en) 2003-09-16 2009-10-13 Boston Scientific Neuromodulation Corporation System and method for lead fixation
US20090287279A1 (en) * 2008-05-15 2009-11-19 Boston Scientific Neuromodulation Corporation Current steering for an implantable stimulator device involving fractionalized stimulation pulses
US20100010582A1 (en) * 2008-07-11 2010-01-14 Boston Scientific Neuromodulation Corporation Medical system and method for setting programmable heat limits
US20100023069A1 (en) * 2008-07-24 2010-01-28 Boston Scientific Neuromodulation Corporation System and method for maintaining a distribution of currents in an electrode array using independent voltage sources
US20100049289A1 (en) * 2007-07-10 2010-02-25 Ams Research Corporation Tissue anchor
US20100076254A1 (en) * 2006-06-05 2010-03-25 Ams Research Corporation Electrical muscle stimulation to treat fecal incontinence and/or pelvic prolapse
US20100087706A1 (en) * 2008-09-30 2010-04-08 Intrapace, Inc. Lead Access
US7702394B2 (en) 2001-05-01 2010-04-20 Intrapace, Inc. Responsive gastric stimulator
US20100137948A1 (en) * 2008-12-03 2010-06-03 Boston Scientific Neuromodulation Corporation External charger with adjustable alignment indicator
US20100217340A1 (en) * 2009-02-23 2010-08-26 Ams Research Corporation Implantable Medical Device Connector System
US20100234917A1 (en) * 2001-05-01 2010-09-16 Intrapace, Inc. Digestive Organ Retention Device
US20100305631A1 (en) * 2001-12-04 2010-12-02 Boston Scientific Neuromodulation Corporation Apparatus and method for determining the relative position and orientation of neurostimulation leads
US20110034760A1 (en) * 2009-04-03 2011-02-10 Intrapace, Inc. Feedback systems and methods to enhance obstructive and other obesity treatments
US20110046660A1 (en) * 2009-02-13 2011-02-24 Intrapace, Inc. Endoscopic Forceps With Removable Handle
US7932696B2 (en) 2007-05-14 2011-04-26 Boston Scientific Neuromodulation Corporation Charger alignment indicator with adjustable threshold
US7953497B1 (en) 2002-08-06 2011-05-31 Boston Scientific Neuromodulation Corporation Insertion stylet
US20110160793A1 (en) * 2009-12-31 2011-06-30 Ams Research Corporation Multi-Zone Stimulation Implant System and Method
US7983766B1 (en) 2001-05-29 2011-07-19 Boston Scientific Neuromodulation Corporation Method of securing a neural stimulation lead
US20110298304A1 (en) * 2010-06-07 2011-12-08 Thoratec Corporation Bi-ventricular percutaneous cable
US8224459B1 (en) 2004-04-30 2012-07-17 Boston Scientific Neuromodulation Corporation Insertion tool for paddle-style electrode
US8255057B2 (en) 2009-01-29 2012-08-28 Nevro Corporation Systems and methods for producing asynchronous neural responses to treat pain and/or other patient conditions
US8295945B1 (en) 2001-05-29 2012-10-23 Boston Scientific Neuromodulation Corporation Neural stimulation lead fixation
US8549015B2 (en) 2007-05-01 2013-10-01 Giancarlo Barolat Method and system for distinguishing nociceptive pain from neuropathic pain
US8706259B2 (en) 2004-04-30 2014-04-22 Boston Scientific Neuromodulation Corporation Insertion tool for paddle-style electrode
US8934976B2 (en) 2004-09-23 2015-01-13 Intrapace, Inc. Feedback systems and methods to enhance obstructive and other obesity treatments, optionally using multiple sensors
US9220887B2 (en) 2011-06-09 2015-12-29 Astora Women's Health LLC Electrode lead including a deployable tissue anchor
US9308378B2 (en) 2013-05-03 2016-04-12 Alfred E. Mann Foundation For Scientific Research Implant recharger handshaking system and method
US9427574B2 (en) 2014-08-15 2016-08-30 Axonics Modulation Technologies, Inc. Implantable lead affixation structure for nerve stimulation to alleviate bladder dysfunction and other indication
US9427573B2 (en) 2007-07-10 2016-08-30 Astora Women's Health, Llc Deployable electrode lead anchor
US9433779B2 (en) 2013-05-03 2016-09-06 Alfred E. Mann Foundation For Scientific Research Multi-branch stimulation electrode for subcutaneous field stimulation
US9446241B2 (en) 2013-03-15 2016-09-20 Alfred E. Mann Foundation For Scientific Research Current sensing multiple output current stimulators
US9517338B1 (en) 2016-01-19 2016-12-13 Axonics Modulation Technologies, Inc. Multichannel clip device and methods of use
US9533155B2 (en) 2014-08-15 2017-01-03 Axonics Modulation Technologies, Inc. Methods for determining neurostimulation electrode configurations based on neural localization
US9539433B1 (en) 2009-03-18 2017-01-10 Astora Women's Health, Llc Electrode implantation in a pelvic floor muscular structure
US9555246B2 (en) 2014-08-15 2017-01-31 Axonics Modulation Technologies, Inc. Electromyographic lead positioning and stimulation titration in a nerve stimulation system for treatment of overactive bladder
US9668690B1 (en) 2001-05-01 2017-06-06 Intrapace, Inc. Submucosal gastric implant device and method
US9675807B2 (en) 2013-05-03 2017-06-13 Alfred E. Mann Foundation For Scientific Research High reliability wire welding for implantable devices
US9682237B2 (en) 2013-03-15 2017-06-20 Alfred E. Mann Foundation For Scientific Research High voltage monitoring successive approximation analog to digital converter
US9700731B2 (en) 2014-08-15 2017-07-11 Axonics Modulation Technologies, Inc. Antenna and methods of use for an implantable nerve stimulator
US9728981B2 (en) 2012-08-31 2017-08-08 Alfred E. Mann Foundation For Scientific Research Feedback controlled coil driver for inductive power transfer
US9731112B2 (en) 2011-09-08 2017-08-15 Paul J. Gindele Implantable electrode assembly
US9780596B2 (en) 2013-07-29 2017-10-03 Alfred E. Mann Foundation For Scientific Research Microprocessor controlled class E driver
US9802051B2 (en) 2014-08-15 2017-10-31 Axonics Modulation Technologies, Inc. External pulse generator device and associated methods for trial nerve stimulation
US9855436B2 (en) 2013-07-29 2018-01-02 Alfred E. Mann Foundation For Scientific Research High efficiency magnetic link for implantable devices
US9867981B2 (en) 2013-12-04 2018-01-16 Boston Scientific Neuromodulation Corporation Insertion tool for implanting a paddle lead and methods and systems utilizing the tool
US9895546B2 (en) 2015-01-09 2018-02-20 Axonics Modulation Technologies, Inc. Patient remote and associated methods of use with a nerve stimulation system
US9925381B2 (en) 2015-07-10 2018-03-27 Axonics Modulation Technologies, Inc. Implantable nerve stimulator having internal electronics without ASIC and methods of use
US9956000B2 (en) 2015-01-13 2018-05-01 Boston Scientific Neuromodulation Corporation Insertion tool for implanting a paddle lead and methods and systems utilizing the tool
US10092762B2 (en) 2014-08-15 2018-10-09 Axonics Modulation Technologies, Inc. Integrated electromyographic clinician programmer for use with an implantable neurostimulator
US10195423B2 (en) 2016-01-19 2019-02-05 Axonics Modulation Technologies, Inc. Multichannel clip device and methods of use
US10376704B2 (en) 2016-02-12 2019-08-13 Axonics Modulation Technologies, Inc. External pulse generator device and associated methods for trial nerve stimulation
US10561835B2 (en) 2006-10-31 2020-02-18 Medtronic, Inc. Implantable medical lead with threaded fixation
US10603500B2 (en) 2016-01-29 2020-03-31 Axonics Modulation Technologies, Inc. Methods and systems for frequency adjustment to optimize charging of implantable neurostimulator
US10682521B2 (en) 2014-08-15 2020-06-16 Axonics Modulation Technologies, Inc. Attachment devices and associated methods of use with a nerve stimulation charging device
US11110283B2 (en) 2018-02-22 2021-09-07 Axonics, Inc. Neurostimulation leads for trial nerve stimulation and methods of use
US11318310B1 (en) 2015-10-26 2022-05-03 Nevro Corp. Neuromodulation for altering autonomic functions, and associated systems and methods
US11439829B2 (en) 2019-05-24 2022-09-13 Axonics, Inc. Clinician programmer methods and systems for maintaining target operating temperatures
US11484723B2 (en) 2015-01-09 2022-11-01 Axonics, Inc. Attachment devices and associated methods of use with a nerve stimulation charging device
US11590352B2 (en) 2019-01-29 2023-02-28 Nevro Corp. Ramped therapeutic signals for modulating inhibitory interneurons, and associated systems and methods
US11642537B2 (en) 2019-03-11 2023-05-09 Axonics, Inc. Charging device with off-center coil
US11848090B2 (en) 2019-05-24 2023-12-19 Axonics, Inc. Trainer for a neurostimulator programmer and associated methods of use with a neurostimulation system

Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US1597061A (en) * 1924-10-20 1926-08-24 James A Cultra Electrotherapeutic appliance
US2065295A (en) * 1935-05-16 1936-12-22 Arthur G Sullivan Therapeutic appliance
US2838672A (en) * 1954-06-29 1958-06-10 Physical Medicine Products Co Electro-therapy generator
US3195540A (en) * 1963-03-29 1965-07-20 Louis C Waller Power supply for body implanted instruments
US3236240A (en) * 1962-09-06 1966-02-22 Univ Minnesota Implantable bladder stimulator
US3279468A (en) * 1963-05-14 1966-10-18 Vine Sidney Le Electrotherapeutic facial mask apparatus
US3405715A (en) * 1966-10-20 1968-10-15 Medtronic Inc Implantable electrode

Patent Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US1597061A (en) * 1924-10-20 1926-08-24 James A Cultra Electrotherapeutic appliance
US2065295A (en) * 1935-05-16 1936-12-22 Arthur G Sullivan Therapeutic appliance
US2838672A (en) * 1954-06-29 1958-06-10 Physical Medicine Products Co Electro-therapy generator
US3236240A (en) * 1962-09-06 1966-02-22 Univ Minnesota Implantable bladder stimulator
US3195540A (en) * 1963-03-29 1965-07-20 Louis C Waller Power supply for body implanted instruments
US3279468A (en) * 1963-05-14 1966-10-18 Vine Sidney Le Electrotherapeutic facial mask apparatus
US3405715A (en) * 1966-10-20 1968-10-15 Medtronic Inc Implantable electrode

Cited By (445)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3727616A (en) * 1971-06-15 1973-04-17 Gen Dynamics Corp Electronic system for the stimulation of biological systems
FR2196783A1 (en) * 1972-08-28 1974-03-22 Areca
US3851651A (en) * 1972-12-22 1974-12-03 P Icenbice Facial stimulating apparatus having sequentially energized electrodes
US3888261A (en) * 1973-12-07 1975-06-10 Medtronic Inc Time shared stimulator
DE2457850A1 (en) * 1973-12-07 1975-06-12 Medtronic Inc CIRCUIT ARRANGEMENT FOR STIMULATING A BIOLOGICAL SYSTEM
US3893463A (en) * 1973-12-07 1975-07-08 Medtronic Inc Dual channel stimulator
US3955560A (en) * 1974-06-10 1976-05-11 Stein Richard B Implantable neural electrode
US3945387A (en) * 1974-09-09 1976-03-23 General Electric Company Implantable cardiac pacer with characteristic controllable circuit and control device therefor
FR2320762A1 (en) * 1975-08-11 1977-03-11 Medtronic Inc ELECTRICAL STIMULATION AND STIMULATOR DEVICE IMPLANTABLE IN A BODY
US4019518A (en) * 1975-08-11 1977-04-26 Medtronic, Inc. Electrical stimulation system
US4120306A (en) * 1976-01-22 1978-10-17 Vitatron Medical B.V. Cardiac pacer with pre-programmed power source interface means
DE2742956A1 (en) * 1976-09-27 1978-03-30 Harry Henry Dr Leveen DEVICE FOR TREATMENT OF DISEASES IN ANIMALS WITH HIGH FREQUENCY RADIANT ENERGY
US4095602A (en) * 1976-09-27 1978-06-20 Leveen Harry H Multi-portal radiofrequency generator
US4157087A (en) * 1978-03-06 1979-06-05 Med General, Inc. Peripheral nerve stimulator
DE2811463A1 (en) * 1978-03-18 1979-09-20 Inst Kib Akademii Nauk Uk Ssr ELECTRIC STIMULATOR FOR HUMAN MUSCLES WITH BIOELECTRIC CONTROL
DE2926861A1 (en) * 1978-07-03 1980-01-24 Technion Res & Dev Foundation THROUGH THE SKIN-WORKING ARRANGEMENT TO REDUCE PAIN
US4256116A (en) * 1978-07-03 1981-03-17 Technion Research And Development Foundation, Limited Transcutaneous pain reliever
DK152609B (en) * 1979-07-04 1988-03-28 Sp Ni Ok Apparatus for electrical stimulation
DE2929293A1 (en) * 1979-07-11 1981-02-05 Sp Ni Ok Bjuro Marijskogo Resp DEVICE FOR ELECTRICALLY INFLUENCING MILK Glands
US4340063A (en) * 1980-01-02 1982-07-20 Empi, Inc. Stimulation device
US4442839A (en) * 1981-04-27 1984-04-17 Empi, Inc. Method of modulating energy in train of electrical pulses
US4431002A (en) * 1981-06-08 1984-02-14 Empi Inc. Modulated deep afferent stimulator
US4456012A (en) * 1982-02-22 1984-06-26 Medtronic, Inc. Iontophoretic and electrical tissue stimulation device
US4708145A (en) * 1982-06-01 1987-11-24 Medtronic, Inc. Sequential-pulse, multiple pathway defibrillation method
US5105811A (en) * 1982-07-27 1992-04-21 Commonwealth Of Australia Cochlear prosthetic package
US4585005A (en) * 1984-04-06 1986-04-29 Regents Of University Of California Method and pacemaker for stimulating penile erection
US4567900A (en) * 1984-06-04 1986-02-04 Moore J Paul Internal deployable defibrillator electrode
US4569351A (en) * 1984-12-20 1986-02-11 University Of Health Sciences/The Chicago Medical School Apparatus and method for stimulating micturition and certain muscles in paraplegic mammals
US4592359A (en) * 1985-04-02 1986-06-03 The Board Of Trustees Of The Leland Stanford Junior University Multi-channel implantable neural stimulator
US4763656A (en) * 1985-06-13 1988-08-16 Beatrice T. Kester Transcutaneous electrical nerve stimulation device and method
US4690146A (en) * 1985-06-17 1987-09-01 Chattanooga Corporation Neuromuscular stimulating apparatus
EP0234457A2 (en) * 1986-02-24 1987-09-02 Medtronic, Inc. Intramuscular lead
EP0234457A3 (en) * 1986-02-24 1988-05-25 Medtronic, Inc. Intramuscular lead
US4841973A (en) * 1987-09-21 1989-06-27 Stecker Harold D Electrical stimulators
US5121754A (en) * 1990-08-21 1992-06-16 Medtronic, Inc. Lateral displacement percutaneously inserted epidural lead
US5281219A (en) * 1990-11-23 1994-01-25 Medtronic, Inc. Multiple stimulation electrodes
US5425752A (en) * 1991-11-25 1995-06-20 Vu'nguyen; Dung D. Method of direct electrical myostimulation using acupuncture needles
US5358514A (en) * 1991-12-18 1994-10-25 Alfred E. Mann Foundation For Scientific Research Implantable microdevice with self-attaching electrodes
US5324316A (en) * 1991-12-18 1994-06-28 Alfred E. Mann Foundation For Scientific Research Implantable microstimulator
US5193540A (en) * 1991-12-18 1993-03-16 Alfred E. Mann Foundation For Scientific Research Structure and method of manufacture of an implantable microstimulator
US5405367A (en) * 1991-12-18 1995-04-11 Alfred E. Mann Foundation For Scientific Research Structure and method of manufacture of an implantable microstimulator
US5193539A (en) * 1991-12-18 1993-03-16 Alfred E. Mann Foundation For Scientific Research Implantable microstimulator
US5447526A (en) * 1992-12-24 1995-09-05 Karsdon; Jeffrey Transcutaneous electric muscle/nerve controller/feedback unit
US5713940A (en) * 1992-12-24 1998-02-03 Jeffrey Karsdon Transcutaneous electric muscle/nerve controller/feedback unit
US5291902A (en) * 1993-01-11 1994-03-08 Brent Carman Incontinence treatment
US5643330A (en) * 1994-01-24 1997-07-01 Medtronic, Inc. Multichannel apparatus for epidural spinal cord stimulation
US5501703A (en) * 1994-01-24 1996-03-26 Medtronic, Inc. Multichannel apparatus for epidural spinal cord stimulator
US5524624A (en) * 1994-05-05 1996-06-11 Amei Technologies Inc. Apparatus and method for stimulating tissue growth with ultrasound
US5833714A (en) * 1996-01-18 1998-11-10 Loeb; Gerald E. Cochlear electrode array employing tantalum metal
US7127297B2 (en) 1996-06-07 2006-10-24 Advanced Neuromodulation Systems, Inc. Multiprogrammable tissue stimulator and method
US7254445B2 (en) 1996-06-07 2007-08-07 Advanced Neuromodulation Systems, Inc. Multiprogrammable tissue stimulator and method
US20050090876A1 (en) * 1996-06-07 2005-04-28 Jay Law Multiprogrammable tissue stimulator and method
US20030195591A1 (en) * 1996-06-07 2003-10-16 Jay Law Multiprogrammable tissue stimulator and method
WO1998009679A1 (en) * 1996-09-05 1998-03-12 The Governors Of The University Of Alberta Gastro-intestinal electrical pacemaker
US6449511B1 (en) 1996-09-05 2002-09-10 University Technologies International Inc. Gastrointestinal electrical stimulator having a variable electrical stimulus
US6243607B1 (en) 1996-09-05 2001-06-05 University Technologies International Inc. Gastro-intestinal electrical pacemaker
US6026326A (en) * 1997-01-13 2000-02-15 Medtronic, Inc. Apparatus and method for treating chronic constipation
WO1998030280A1 (en) * 1997-01-13 1998-07-16 Medtronic, Inc. Apparatus and method for treating chronic constipation
US5957958A (en) * 1997-01-15 1999-09-28 Advanced Bionics Corporation Implantable electrode arrays
US6941171B2 (en) 1998-07-06 2005-09-06 Advanced Bionics Corporation Implantable stimulator methods for treatment of incontinence and pain
US6735474B1 (en) 1998-07-06 2004-05-11 Advanced Bionics Corporation Implantable stimulator system and method for treatment of incontinence and pain
US9050473B2 (en) 1999-01-07 2015-06-09 Boston Sceintific Neuromodulation Corporation System for normalizing amplitude programming of a tissue stimulator
US8805524B2 (en) 1999-01-07 2014-08-12 Boston Scientific Neuromodulation Corporation System and method for displaying stimulation field generated by electrode array
US20080215119A1 (en) * 1999-01-07 2008-09-04 Boston Scientific Neuromodulation Corporation System and method for displaying stimulation field generated by electrode array
US20110060386A1 (en) * 1999-01-07 2011-03-10 Boston Scientific Neuromodulation Corporation System and method for displaying stimulation field generated by electrode array
US8265762B2 (en) 1999-01-07 2012-09-11 Boston Scientific Neuromodulation Corporation Implantable pulse generator having current steering means
US7930030B2 (en) 1999-01-07 2011-04-19 Boston Scientific Neuromodulation Corporation Implantable pulse generator having current steering means
US7555346B1 (en) 1999-01-07 2009-06-30 Boston Scientific Neuromodulation Corporation Implantable pulse generator having current steering means
US8121701B2 (en) 1999-01-07 2012-02-21 Boston Scientific Neuromodulation Corporation System and method for displaying stimulation field generated by electrode array
US8401658B2 (en) 1999-01-07 2013-03-19 Boston Scientific Neuromodulation Corporation System and method for displaying stimulation field generated by electrode array
US20080221637A1 (en) * 1999-01-07 2008-09-11 Boston Scientific Neuromodulation Corporation Implantable pulse generator having current steering means
US20040147976A1 (en) * 1999-04-14 2004-07-29 Transneuronix, Inc. Gastric stimulator apparatus and method for installing
US6542776B1 (en) * 1999-04-14 2003-04-01 Transneuronix Inc. Gastric stimulator apparatus and method for installing
US6684104B2 (en) 1999-04-14 2004-01-27 Transneuronix, Inc. Gastric stimulator apparatus and method for installing
US6606523B1 (en) * 1999-04-14 2003-08-12 Transneuronix Inc. Gastric stimulator apparatus and method for installing
US9907957B2 (en) 1999-07-27 2018-03-06 Boston Scientific Neuromodulation Corporation Patient programmer for implantable devices
US20070276450A1 (en) * 1999-07-27 2007-11-29 Advanced Bionics Corporation Rechargeable spinal cord stimulation system
US7496404B2 (en) 1999-07-27 2009-02-24 Boston Scientific Neuromodulation Corporation Rechargeable spinal cord stimulator system
US6516227B1 (en) 1999-07-27 2003-02-04 Advanced Bionics Corporation Rechargeable spinal cord stimulator system
US20070293914A1 (en) * 1999-07-27 2007-12-20 Advanced Bionics Corporation Patient programmer for implantable devices
US8918174B2 (en) 1999-07-27 2014-12-23 Boston Scientific Neuromodulation Corporation Patient programmer for implantable devices
US7769462B2 (en) 1999-07-27 2010-08-03 Boston Scientific Neuromodulation Corporation Rechargeable spinal cord stimulation system
US7801615B2 (en) 1999-07-27 2010-09-21 Boston Scientific Neuromodulation Corporation Rechargeable spinal cord stimulator system
US6895280B2 (en) 1999-07-27 2005-05-17 Advanced Bionics Corporation Rechargeable spinal cord stimulator system
US20030191504A1 (en) * 1999-07-30 2003-10-09 Meadows Paul M. Implantable pulse generators using rechargeable zero-volt technology lithium-ion batteries
US20070185551A1 (en) * 1999-07-30 2007-08-09 Advanced Bionics Corporation Implantable Pulse Generators Using Rechargeable Zero-Volt Technology Lithium-Ion Batteries
US7818068B2 (en) 1999-07-30 2010-10-19 Boston Scientific Neuromodulation Corporation Implantable pulse generators using rechargeable zero-volt technology lithium-ion batteries
US7177691B2 (en) 1999-07-30 2007-02-13 Advanced Bionics Corporation Implantable pulse generators using rechargeable zero-volt technology lithium-ion batteries
US7184836B1 (en) 1999-07-30 2007-02-27 Advanced Bionics Corporation Implantable devices using rechargeable zero-volt technology lithium-ion batteries
US7295878B1 (en) 1999-07-30 2007-11-13 Advanced Bionics Corporation Implantable devices using rechargeable zero-volt technology lithium-ion batteries
US6381496B1 (en) 1999-10-01 2002-04-30 Advanced Bionics Corporation Parameter context switching for an implanted device
US7319904B2 (en) 2000-02-08 2008-01-15 Medtronic, Inc. Percutaneous Surgical lead body
US20030229387A1 (en) * 2000-02-08 2003-12-11 Medtronic, Inc. Surgical lead body
US6659968B1 (en) 2000-06-01 2003-12-09 Advanced Bionics Corporation Activity monitor for pain management efficacy measurement
EP2002861A2 (en) 2000-07-26 2008-12-17 Boston Scientific Neuromodulation Corporation Rechargeable stimulator system
EP2752221A2 (en) 2000-07-26 2014-07-09 Boston Scientific Neuromodulation Corporation Rechargeable spinal cord stimulator system
WO2002009808A1 (en) 2000-07-26 2002-02-07 Advanced Bionics Corporation Rechargeable spinal cord stimulator system
EP2277586A2 (en) 2000-07-26 2011-01-26 Boston Scientific Neuromodulation Corporation Regarcheable spinal cord stimulator system
US8214048B1 (en) 2000-08-18 2012-07-03 Boston Scientific Neuromodulation Corporation Fully implantable neurostimulator for autonomic nerve fiber stimulation as a therapy for urinary and bowel dysfunction
US6871099B1 (en) 2000-08-18 2005-03-22 Advanced Bionics Corporation Fully implantable microstimulator for spinal cord stimulation as a therapy for chronic pain
US8588917B2 (en) 2000-08-18 2013-11-19 Boston Scientific Neuromodulation Corporation Fully implantable neurostimulator for autonomic nerve fiber stimulation as a therapy for urinary and bowel dysfunction
US7054689B1 (en) 2000-08-18 2006-05-30 Advanced Bionics Corporation Fully implantable neurostimulator for autonomic nerve fiber stimulation as a therapy for urinary and bowel dysfunction
US20050119713A1 (en) * 2000-08-18 2005-06-02 Whitehurst Todd K. Methods for implanting a spinal cord stimulator
WO2002038217A3 (en) * 2000-11-09 2002-10-31 Neuropace Inc Implantable neuromuscular stimulator for the treatment of gastrointestinal disorders
US7212867B2 (en) 2000-12-07 2007-05-01 Medtronic, Inc. Directional brain stimulation and recording leads
US20020183817A1 (en) * 2000-12-07 2002-12-05 Paul Van Venrooij Directional brain stimulation and recording leads
US7009313B1 (en) 2001-03-16 2006-03-07 Advanced Bionics Corporation Multi-compliance voltage generator in a multichannel current stimulator
US7120498B2 (en) 2001-05-01 2006-10-10 Intrapace, Inc. Method and device for securing a functional device to a stomach
US7483754B2 (en) 2001-05-01 2009-01-27 Intrapace, Inc. Endoscopic instrument system for implanting a device in the stomach
US7643887B2 (en) 2001-05-01 2010-01-05 Intrapace, Inc. Abdominally implanted stimulator and method
US20090299434A1 (en) * 2001-05-01 2009-12-03 Intrapace, Inc. Endoscopic System For Attaching a Device to a Stomach
US8019422B2 (en) 2001-05-01 2011-09-13 Intrapace, Inc. Gastric device and endoscopic delivery system
US7590452B2 (en) 2001-05-01 2009-09-15 Intrapace, Inc. Endoscopic system for attaching a device to a stomach
US7107100B2 (en) 2001-05-01 2006-09-12 Intrapace, Inc. Aendoscopic instrument system@
US7979127B2 (en) 2001-05-01 2011-07-12 Intrapace, Inc. Digestive organ retention device
US20030164304A1 (en) * 2001-05-01 2003-09-04 Imran Mir A. Aendoscopic instrument system@
US20060116735A1 (en) * 2001-05-01 2006-06-01 Imran Mir A Gastric device and endoscopic delivery system
US20060111753A1 (en) * 2001-05-01 2006-05-25 Imran Mir A Gastric stimulation anchor and method
US20030167025A1 (en) * 2001-05-01 2003-09-04 Imran Mir A. Gastric treatment/diagnosis device and attachment device and method
US8190261B2 (en) 2001-05-01 2012-05-29 Intrapace, Inc. Gastrointestinal anchor in optimal surface area
US9668690B1 (en) 2001-05-01 2017-06-06 Intrapace, Inc. Submucosal gastric implant device and method
US20090099415A1 (en) * 2001-05-01 2009-04-16 Intrapace, Inc. Endoscopic Instrument System for Implanting a Device in the Stomach
US7509174B2 (en) 2001-05-01 2009-03-24 Intrapace, Inc. Gastric treatment/diagnosis device and attachment device and method
US20090018605A1 (en) * 2001-05-01 2009-01-15 Intrapace, Inc. Gastric Treatment/Diagnosis Device and Attachment Device and Method
US20040243195A1 (en) * 2001-05-01 2004-12-02 Imran Mir A. Endoscopic system for attaching a device to a stomach
US8364269B2 (en) 2001-05-01 2013-01-29 Intrapace, Inc. Responsive gastric stimulator
US7689284B2 (en) 2001-05-01 2010-03-30 Intrapace, Inc. Pseudounipolar lead for stimulating a digestive organ
US9517152B2 (en) 2001-05-01 2016-12-13 Intrapace, Inc. Responsive gastric stimulator
US7076305B2 (en) 2001-05-01 2006-07-11 Intrapace, Inc. Gastric device and instrument system and method
US20060089699A1 (en) * 2001-05-01 2006-04-27 Imran Mir A Abdominally implanted stimulator and method
US20020165589A1 (en) * 2001-05-01 2002-11-07 Imran Mir A. Gastric treatment and diagnosis device and method
US20060074458A1 (en) * 2001-05-01 2006-04-06 Imran Mir A Digestive organ retention device
US20100234917A1 (en) * 2001-05-01 2010-09-16 Intrapace, Inc. Digestive Organ Retention Device
US20050143784A1 (en) * 2001-05-01 2005-06-30 Imran Mir A. Gastrointestinal anchor with optimal surface area
US7371215B2 (en) 2001-05-01 2008-05-13 Intrapace, Inc. Endoscopic instrument for engaging a device
US7702394B2 (en) 2001-05-01 2010-04-20 Intrapace, Inc. Responsive gastric stimulator
US20080065169A1 (en) * 2001-05-01 2008-03-13 Intrapace, Inc. Endoscopic Instrument for Engaging a Device
US20060074457A1 (en) * 2001-05-01 2006-04-06 Imran Mir A Pseudounipolar lead for stimulating a digestive organ
US20050236277A9 (en) * 2001-05-01 2005-10-27 Imran Mir A Aendoscopic instrument system@
US7747322B2 (en) 2001-05-01 2010-06-29 Intrapace, Inc. Digestive organ retention device
US20100305656A1 (en) * 2001-05-01 2010-12-02 Intrapace, Inc. Gastric Simulation Anchor and Method
US20060069414A1 (en) * 2001-05-01 2006-03-30 Imran Mir A Endoscopic instrument system for implanting a device in the stomach
US7756582B2 (en) 2001-05-01 2010-07-13 Intrapace, Inc. Gastric stimulation anchor and method
US7016735B2 (en) 2001-05-01 2006-03-21 Intrapace, Inc. Gastric anchor and method
US7020531B1 (en) 2001-05-01 2006-03-28 Intrapace, Inc. Gastric device and suction assisted method for implanting a device on a stomach wall
US7099718B1 (en) 2001-05-29 2006-08-29 Advanced Bionics Corporation Neural stimulation lead fixation
US8295945B1 (en) 2001-05-29 2012-10-23 Boston Scientific Neuromodulation Corporation Neural stimulation lead fixation
US7856277B1 (en) 2001-05-29 2010-12-21 Boston Scientific Neuromodulation Corporation Neural stimulation lead fixation
US7983766B1 (en) 2001-05-29 2011-07-19 Boston Scientific Neuromodulation Corporation Method of securing a neural stimulation lead
US8554342B2 (en) 2001-05-29 2013-10-08 Boston Scientific Neuromodulation Corporation Neural stimulation lead fixation
US20050055063A1 (en) * 2001-07-20 2005-03-10 Loeb Gerald E. Method and apparatus for the treatment of urinary tract dysfunction
US20090281599A1 (en) * 2001-08-13 2009-11-12 Boston Scientific Neuromodulation Corporation System and method of rapid, comfortable parameter switching in spinal cord stimulation
US7571001B2 (en) 2001-08-13 2009-08-04 Boston Scientific Neuromodulation Corporation System and method of rapid, comfortable parameter switching in spinal cord stimulation
US8036747B2 (en) 2001-08-13 2011-10-11 Boston Scientific Neuromodulation Corporation System and method of rapid, comfortable parameter switching in spinal cord stimulation
US7263402B2 (en) 2001-08-13 2007-08-28 Advanced Bionics Corporation System and method of rapid, comfortable parameter switching in spinal cord stimulation
US20030032992A1 (en) * 2001-08-13 2003-02-13 Thacker James R. System and method of rapid, Comfortable parameter switching in spinal cord stimulation
US20030078633A1 (en) * 2001-09-28 2003-04-24 Firlik Andrew D. Methods and implantable apparatus for electrical therapy
US7127296B2 (en) 2001-11-02 2006-10-24 Advanced Bionics Corporation Method for increasing the therapeutic ratio/usage range in a neurostimulator
US20030093134A1 (en) * 2001-11-02 2003-05-15 Kerry Bradley Method for increasing the therapeutic ratio/usage range in a neurostimulator
US20090036946A1 (en) * 2001-11-29 2009-02-05 American Medical Systems, Inc. Pelvic disorder treatments
US7853330B2 (en) 2001-12-04 2010-12-14 Boston Scientific Neuromodulation Corporation Apparatus and method for determining the relative position and orientation of neurostimulation leads
US8682447B2 (en) 2001-12-04 2014-03-25 Boston Scientific Neuromodulation Corporation Apparatus and method for determining the relative position and orientation of neurostimulation leads
US20060122653A1 (en) * 2001-12-04 2006-06-08 Kerry Bradley Apparatus and method for determining the relative position and orientation of neurostimulation leads
US7684869B2 (en) 2001-12-04 2010-03-23 Boston Scientific Neuromodulation Corporation Apparatus and method for determining the relative position and orientation of neurostimulation leads
US9610439B2 (en) 2001-12-04 2017-04-04 Boston Scientific Neuromodulation Corporation Apparatus and method for determining the relative position and orientation of neurostimulation leads
US9192760B2 (en) 2001-12-04 2015-11-24 Boston Scientific Neuromodulation Corporation Apparatus and method for determining the relative position and orientation of neurostimulation leads
US20100305631A1 (en) * 2001-12-04 2010-12-02 Boston Scientific Neuromodulation Corporation Apparatus and method for determining the relative position and orientation of neurostimulation leads
US20060122654A1 (en) * 2001-12-04 2006-06-08 Kerry Bradley Apparatus and method for determining the relative position and orientation of neurostimulation leads
US10022540B2 (en) 2001-12-04 2018-07-17 Boston Scientific Neuromodulation Corporation Apparatus and method for determining the relative position and orientation of neurostimulation leads
US20070265679A1 (en) * 2002-02-04 2007-11-15 Advanced Bionics Corporation Method for optimizing search for spinal cord stimulation parameter setting
US7881805B2 (en) 2002-02-04 2011-02-01 Boston Scientific Neuromodulation Corporation Method for optimizing search for spinal cord stimulation parameter settings
US9227065B2 (en) 2002-02-04 2016-01-05 Boston Scientific Neuromodulation Corporation Method for programming implantable device
US9687653B2 (en) 2002-02-04 2017-06-27 Boston Scientific Neuromodulation Corporation Method for programming implantabale device
US20080071325A1 (en) * 2002-02-04 2008-03-20 Advanced Bionics Corporation Method for optimizing search for spinal cord stimulation parameter setting
US8233991B2 (en) 2002-02-04 2012-07-31 Boston Scientific Neuromodulation Corporation Method for programming implantable device
US8065013B2 (en) 2002-02-04 2011-11-22 Boston Scientific Neuromodulation Corporation Method for optimizing search for spinal cord stimulation parameter setting
US20050245987A1 (en) * 2002-02-04 2005-11-03 Woods Carla M Method for programming implantable device
US7991482B2 (en) 2002-02-04 2011-08-02 Boston Scientific Neuromodulation Corporation Method for optimizing search for spinal cord stimulation parameter setting
US7146223B1 (en) 2002-02-04 2006-12-05 Advanced Bionics Corporation Method for optimizing search for spinal cord stimulation parameter settings
US7801621B1 (en) 2002-02-12 2010-09-21 Boston Scientific Neuromodulation Corporation Neural stimulation system providing auto adjustment of stimulus output as a function of sensed pressure changes
US20100262209A1 (en) * 2002-02-12 2010-10-14 Boston Scientific Neuromodulation Corporation Neural stimulation system providing auto adjustment of stimulus output as a function of sensed impedance
US8788056B2 (en) 2002-02-12 2014-07-22 Boston Scientific Neuromodulation Corporation Neural stimulation system providing auto adjustment of stimulus output as a function of sensed impedance
US7742823B2 (en) 2002-02-12 2010-06-22 Boston Scientific Neuromodulation Corporation Neural stimulation system providing auto adjustment of stimulus output as a function of sensed impedance
US7239920B1 (en) 2002-02-12 2007-07-03 Advanced Bionics Corporation Neural stimulation system providing auto adjustment of stimulus output as a function of sensed pressure changes
US7317948B1 (en) 2002-02-12 2008-01-08 Boston Scientific Scimed, Inc. Neural stimulation system providing auto adjustment of stimulus output as a function of sensed impedance
US8626312B2 (en) 2002-02-12 2014-01-07 Boston Scientific Neuromodulation Corporation Neural stimulation system providing auto adjustment of stimulus output as a function of sensed impedance
US9089706B2 (en) 2002-02-12 2015-07-28 Boston Scientific Neuromodulation Corporation Neural stimulation system providing auto adjustment of stimulus output as a function of sensed impedance
US9205263B2 (en) 2002-02-12 2015-12-08 Boston Scientific Neuromodulation Corporation Neural stimulation system providing auto adjustment of stimulus output as a function of sensed impedance
US20030153959A1 (en) * 2002-02-12 2003-08-14 Thacker James R. Neural stimulation system providing auto adjustment of stimulus output as a function of sensed coupling efficiency
US20110060387A1 (en) * 2002-02-12 2011-03-10 Boston Scientific Neuromodulation Corporation Neural stimulation system providing auto adjustment of stimulus output as a function of sensed impedance
US7953497B1 (en) 2002-08-06 2011-05-31 Boston Scientific Neuromodulation Corporation Insertion stylet
US7363079B1 (en) 2002-09-26 2008-04-22 Boston Scientific Neuromodulation Corporation Power qualifier for electrical stimulation configurations
US7127298B1 (en) 2002-10-18 2006-10-24 Advanced Bionics Corporation Switched-matrix output for multi-channel implantable stimulator
US7797057B2 (en) 2002-10-23 2010-09-14 Medtronic, Inc. Medical paddle lead and method for spinal cord stimulation
US20040260310A1 (en) * 2002-10-23 2004-12-23 Medtronic, Inc. Medical lead and method
US20050182470A1 (en) * 2002-10-23 2005-08-18 Medtronic, Inc. Paddle-style medical lead and method
US7499755B2 (en) 2002-10-23 2009-03-03 Medtronic, Inc. Paddle-style medical lead and method
US7174215B2 (en) 2002-12-06 2007-02-06 Advanced Bionics Corporation Method for determining stimulation parameters
US20040116978A1 (en) * 2002-12-06 2004-06-17 Kerry Bradley Method for determining stimulation parameters
US20040158170A1 (en) * 2003-02-04 2004-08-12 Overstreet Edward H. Method of rapid neural response measurement without amplitude attenuation
US7277759B2 (en) 2003-02-04 2007-10-02 Advanced Bionics Corporation Method of rapid neural response measurement without amplitude attenuation
US7162304B1 (en) 2003-05-08 2007-01-09 Advanced Bionics Corporation System for measuring cardiac rhythm parameters for assessment of spinal cord stimulation
US20070083240A1 (en) * 2003-05-08 2007-04-12 Peterson David K L Methods and systems for applying stimulation and sensing one or more indicators of cardiac activity with an implantable stimulator
US20060287686A1 (en) * 2003-07-03 2006-12-21 Advanced Neuromodulation Systems, Inc. System and method for implantable device with one or more stored treatment protocols and transmission to external device
US20050004622A1 (en) * 2003-07-03 2005-01-06 Advanced Neuromodulation Systems System and method for implantable pulse generator with multiple treatment protocols
US7603179B1 (en) 2003-09-16 2009-10-13 Boston Scientific Neuromodulation Corporation System and method for lead fixation
US8285397B2 (en) 2003-09-16 2012-10-09 Boston Scientific Neuromodulation Corporation System and method for lead fixation
US20050090885A1 (en) * 2003-10-23 2005-04-28 Medtronic, Inc. Medical lead and manufacturing method therefor
US7437197B2 (en) 2003-10-23 2008-10-14 Medtronic, Inc. Medical lead and manufacturing method therefor
US20060293723A1 (en) * 2003-12-19 2006-12-28 Whitehurst Todd K Skull-mounted electrical stimulation system and method for treating patients
US7769461B2 (en) 2003-12-19 2010-08-03 Boston Scientific Neuromodulation Corporation Skull-mounted electrical stimulation system and method for treating patients
US20110009920A1 (en) * 2003-12-19 2011-01-13 Boston Scientific Neuromodulation Corporation Skull-mounted electrical stimulation system and method for treating patients
US8606367B2 (en) 2004-04-30 2013-12-10 Boston Scientific Neuromodulation Corporation Insertion tool for paddle-style electrode
US8805543B2 (en) 2004-04-30 2014-08-12 Boston Scientific Neuromodulation Corporation Insertion tool for paddle-style electrode
US8805544B2 (en) 2004-04-30 2014-08-12 Boston Scientific Neuromodulation Corporation Insertion tool for paddle-style electrode
US8224459B1 (en) 2004-04-30 2012-07-17 Boston Scientific Neuromodulation Corporation Insertion tool for paddle-style electrode
US8706259B2 (en) 2004-04-30 2014-04-22 Boston Scientific Neuromodulation Corporation Insertion tool for paddle-style electrode
US8750985B2 (en) 2004-05-28 2014-06-10 Boston Scientific Neuromodulation Corporation Low power loss current digital-to-analog converter used in an implantable pulse generator
US7539538B2 (en) 2004-05-28 2009-05-26 Boston Science Neuromodulation Corporation Low power loss current digital-to-analog converter used in an implantable pulse generator
US20090204174A1 (en) * 2004-05-28 2009-08-13 Boston Scientific Neuromodulation Corporation Low Power Loss Current Digital-to-Analog Converter Used in an Implantable Pulse Generator
US9320899B2 (en) 2004-05-28 2016-04-26 Boston Scientific Neuromodulation Corporation Low power loss current digital-to-analog converter used in an implantable pulse generator
US20050267546A1 (en) * 2004-05-28 2005-12-01 Jordi Parramon Low power loss current digital-to-analog converter used in an implantable pulse generator
US8083741B2 (en) 2004-06-07 2011-12-27 Synthes Usa, Llc Orthopaedic implant with sensors
US20060052782A1 (en) * 2004-06-07 2006-03-09 Chad Morgan Orthopaedic implant with sensors
USRE46582E1 (en) 2004-06-07 2017-10-24 DePuy Synthes Products, Inc. Orthopaedic implant with sensors
US20060030918A1 (en) * 2004-08-04 2006-02-09 Chinn Kenny K Operating room lead connector
US7548788B2 (en) 2004-08-04 2009-06-16 Boston Scientific Neuromodulation Corporation Operating room lead connector
US8504172B2 (en) 2004-08-04 2013-08-06 Boston Scientific Neuromodulation Corporation Operating room lead connector
US20090248096A1 (en) * 2004-08-04 2009-10-01 Boston Scientific Neuromodulation Corporation Operating room lead connector
US8239042B2 (en) 2004-08-04 2012-08-07 Boston Scientific Neuromodulation Corporation Operating room lead connector
US8934976B2 (en) 2004-09-23 2015-01-13 Intrapace, Inc. Feedback systems and methods to enhance obstructive and other obesity treatments, optionally using multiple sensors
US9259342B2 (en) 2004-09-23 2016-02-16 Intrapace, Inc. Feedback systems and methods to enhance obstructive and other obesity treatments, optionally using multiple sensors
US9662240B2 (en) 2004-09-23 2017-05-30 Intrapace, Inc. Feedback systems and methods to enhance obstructive and other obesity treatments, optionally using multiple sensors
US20060070334A1 (en) * 2004-09-27 2006-04-06 Blue Hen, Llc Sidewall plank for constructing a trailer and associated trailer sidewall construction
US20060195159A1 (en) * 2004-12-03 2006-08-31 Kerry Bradley System and method for choosing electrodes in an implanted stimulator device
US10537741B2 (en) 2004-12-03 2020-01-21 Boston Scientific Neuromodulation Corporation System and method for choosing electrodes in an implanted stimulator device
US20060168805A1 (en) * 2005-01-31 2006-08-03 Michael Hegland Method of manufacturing a medical lead
US8739403B2 (en) 2005-01-31 2014-06-03 Medtronic, Inc. Method of manufacturing a medical lead
US8000808B2 (en) 2005-01-31 2011-08-16 Medtronic, Inc. Medical lead with segmented electrode
US20060173262A1 (en) * 2005-01-31 2006-08-03 Medtronic, Inc. Medical lead with segmented electrode
US7761985B2 (en) 2005-01-31 2010-07-27 Medtronic, Inc. Method of manufacturing a medical lead
US8401665B2 (en) 2005-04-01 2013-03-19 Boston Scientific Neuromodulation Corporation Apparatus and methods for detecting position and migration of neurostimulation leads
US8131357B2 (en) 2005-04-01 2012-03-06 Boston Scientific Neuromodulation Corporation Apparatus and methods for detecting migration of neurostimulation leads
US9067075B2 (en) 2005-04-01 2015-06-30 Boston Scientific Neuromodulation Corporation Apparatus and methods for detecting migration of neurostimulation leads
US8972023B2 (en) 2005-04-01 2015-03-03 Boston Scientific Neuromodulation Corporation Apparatus and methods for detecting position and migration of neurostimulation leads
US8718757B2 (en) 2005-04-01 2014-05-06 Boston Scientific Neuromodulation Corporation Apparatus and methods for detecting migration of neurostimulation leads
US20060224222A1 (en) * 2005-04-01 2006-10-05 Kerry Bradley Apparatus and methods for detecting migration of neurostimulation leads
US20060224187A1 (en) * 2005-04-01 2006-10-05 Kerry Bradley Apparatus and methods for detecting position and migration of neurostimulation leads
WO2006112852A2 (en) 2005-04-13 2006-10-26 Advanced Bionics Corporation Method for programming implantable device
US20060241721A1 (en) * 2005-04-26 2006-10-26 Sridhar Kothandaraman Display graphics for use in stimulation therapies
US7979119B2 (en) 2005-04-26 2011-07-12 Boston Scientific Neuromodulation Corporation Display graphics for use in stimulation therapies
US7657317B2 (en) 2005-04-26 2010-02-02 Boston Scientific Neuromodulation Corporation Evaluating stimulation therapies and patient satisfaction
US20060241722A1 (en) * 2005-04-26 2006-10-26 Thacker James R Evaluating stimulation therapies and patient satisfaction
US9037249B2 (en) 2005-07-08 2015-05-19 Boston Scientific Neuromodulation Corporation Current generation architecture for an implantable stimulator device having coarse and fine current control
US9956411B2 (en) 2005-07-08 2018-05-01 Boston Scientific Neuromodulation Corporation Current generation architecture for an implantable stimulator device having coarse and fine current control
WO2007008212A1 (en) 2005-07-08 2007-01-18 Advanced Bionics Corporation Current output architecture for an implantable stimulator device
EP2308554A1 (en) 2005-07-08 2011-04-13 Boston Scientific Neuromodulation Corporation Current output architecture for an implantable stimulator device
US20070038250A1 (en) * 2005-07-08 2007-02-15 Yuping He Current output architecture for an implantable stimulator device
US9314617B2 (en) 2005-07-08 2016-04-19 Boston Scientific Neuromodulation Corporation Current output architecture for an implantable stimulator device
US9308371B2 (en) 2005-07-08 2016-04-12 Boston Scientific Neuromodulation Corporation Current generation architecture for an implantable stimulator device having coarse and fine current control
US8606362B2 (en) 2005-07-08 2013-12-10 Boston Scientific Neuromodulation Corporation Current output architecture for an implantable stimulator device
US9931502B2 (en) 2005-07-08 2018-04-03 Boston Scientific Neuromodulation Corporation Current output architecture for an implantable stimulator device
US8620436B2 (en) 2005-07-08 2013-12-31 Boston Scientific Neuromodulation Corporation Current generation architecture for an implantable stimulator device having coarse and fine current control
US8706238B2 (en) 2005-07-08 2014-04-22 Boston Scientific Neuromodulation Corporation Current generation architecture for an implantable stimulator device having coarse and fine current control
US20100286749A1 (en) * 2005-07-08 2010-11-11 Boston Scientific Neuromodulation Corporation Current Generation Architecture for an Implantable Stimulator Device Having Coarse and Fine Current Control
US11452873B2 (en) 2005-07-08 2022-09-27 Boston Scientific Neuromodulation Corporation Current generation architecture for an implantable stimulator device having coarse and fine current control
US20070100399A1 (en) * 2005-07-08 2007-05-03 Advanced Bionics Corporation Current Generation Architecture for an Implantable Stimulator Device Having Coarse and Fine Current Control
EP2077135A2 (en) 2005-07-08 2009-07-08 Boston Scientific Neuromodulation Corporation Current output architecture for an implantable stimulator device
US10744325B2 (en) 2005-07-08 2020-08-18 Boston Scientific Neuromodulation Corporation Current generation architecture for an implantable stimulator device having coarse and fine current control
US10744318B2 (en) 2005-07-08 2020-08-18 Boston Scientific Neuromodulation Corporation Current output architecture for an implantable stimulator device
US20070049990A1 (en) * 2005-08-30 2007-03-01 Klostermann Daniel J Telemetry protocol for ultra low error rates useable in implantable medical devices
US8428745B2 (en) 2005-08-30 2013-04-23 Boston Scientific Neuromodulation Corporation Telemetry protocol for ultra low error rates useable in implantable medical devices
US8265768B2 (en) 2005-08-30 2012-09-11 Boston Scientific Neuromodulation Corporation Telemetry protocol for ultra low error rates useable in implantable medical devices
US20070049991A1 (en) * 2005-08-30 2007-03-01 Klostermann Daniel J Telemetry-based wake up of an implantable medical device
US7725194B2 (en) 2005-08-30 2010-05-25 Boston Scientific Neuromodulation Corporation Telemetry-based wake up of an implantable medical device
US20100023087A1 (en) * 2005-09-01 2010-01-28 Intrapace, Inc. Randomized stimulation of a gastrointestinal organ
US20070049986A1 (en) * 2005-09-01 2007-03-01 Imran Mir A Randomized stimulation of a gastrointestinal organ
US7616996B2 (en) 2005-09-01 2009-11-10 Intrapace, Inc. Randomized stimulation of a gastrointestinal organ
US8032223B2 (en) 2005-09-01 2011-10-04 Intrapace, Inc. Randomized stimulation of a gastrointestinal organ
WO2007030496A1 (en) 2005-09-06 2007-03-15 Advanced Bionics Corporation Ultracapacitor powered implantable pulse generator with dedicated power supply
US20070055308A1 (en) * 2005-09-06 2007-03-08 Haller Matthew I Ultracapacitor powered implantable pulse generator with dedicated power supply
US8175717B2 (en) 2005-09-06 2012-05-08 Boston Scientific Neuromodulation Corporation Ultracapacitor powered implantable pulse generator with dedicated power supply
US20070053466A1 (en) * 2005-09-08 2007-03-08 Klostermann Daniel J Frequency shift keying demodulation technique
US8798754B2 (en) 2005-09-26 2014-08-05 Venturi Group, Llc Neural blocking therapy
US20070073354A1 (en) * 2005-09-26 2007-03-29 Knudson Mark B Neural blocking therapy
US20080154333A1 (en) * 2005-09-26 2008-06-26 Venturi Group, Llc Neural blocking therapy
US20090018606A1 (en) * 2005-10-12 2009-01-15 Intrapace, Inc. Methods and Devices for Stimulation of an Organ with the Use of a Transectionally Placed Guide Wire
WO2007067825A1 (en) 2005-12-07 2007-06-14 Advanced Bionics Corporation Battery protection and zero-volt battery recovery system for an implantable medical device
EP2072080A2 (en) 2005-12-07 2009-06-24 Boston Scientific Neuromodulation Corporation Battery protection and zero-volt battery recovery system for an implantable medical device
US20080319514A1 (en) * 2005-12-14 2008-12-25 Boston Scientific Neuromodulation Corporation Techniques for Sensing and Adjusting a Compliance Voltage in an Implantable Stimulator Device
US8538548B2 (en) 2005-12-14 2013-09-17 Boston Scientific Neuromodulation Corporation Techniques for sensing and adjusting a compliance voltage in an implantable stimulator device
US7444181B2 (en) 2005-12-14 2008-10-28 Boston Scientific Neuromodulation Corporation Techniques for sensing and adjusting a compliance voltage in an implantable stimulator device
US9061152B2 (en) 2005-12-14 2015-06-23 Boston Scientific Neuromodulation Corporation Techniques for sensing and adjusting a compliance voltage in an implantable stimulator device
US8175719B2 (en) 2005-12-14 2012-05-08 Boston Scientific Neuromodulation Corporation Techniques for sensing and adjusting a compliance voltage in an implantable stimulator device
US20070135868A1 (en) * 2005-12-14 2007-06-14 Shi Jess W Techniques for sensing and adjusting a compliance voltage in an implantable stimulator device
US8781598B2 (en) 2005-12-14 2014-07-15 Boston Scientific Neuromodulation Corporation Techniques for sensing and adjusting a compliance voltage in an implantable stimulator device
US20070156207A1 (en) * 2006-01-04 2007-07-05 Sridhar Kothandaraman Expanding single channel stimulator capability on multi-area stimulation programs
US20070260288A1 (en) * 2006-03-03 2007-11-08 Yossi Gross Apparatus for treating stress and urge incontinence
US8195296B2 (en) 2006-03-03 2012-06-05 Ams Research Corporation Apparatus for treating stress and urge incontinence
US9889298B2 (en) 2006-03-03 2018-02-13 Astora Women's Health, Llc Electrode sling for treating stress and urge incontinence
US20090043356A1 (en) * 2006-03-03 2009-02-12 Ams Research Corporation Electrode Sling for Treating Stress and Urge Incontinence
US20090157091A1 (en) * 2006-04-04 2009-06-18 Ams Research Corporation Apparatus for Implanting Neural Stimulation Leads
US20070239228A1 (en) * 2006-04-07 2007-10-11 Kerry Bradley System and method using multiple timing channels for electrode adjustement during set up of an implanted stimulator device
US7805197B2 (en) 2006-04-07 2010-09-28 Boston Scientific Neuromodulation Corporation System and method using multiple timing channels for electrode adjustment during set up of an implanted stimulator device
US20070265675A1 (en) * 2006-05-09 2007-11-15 Ams Research Corporation Testing Efficacy of Therapeutic Mechanical or Electrical Nerve or Muscle Stimulation
US20100076254A1 (en) * 2006-06-05 2010-03-25 Ams Research Corporation Electrical muscle stimulation to treat fecal incontinence and/or pelvic prolapse
US20080009914A1 (en) * 2006-07-10 2008-01-10 Ams Research Corporation Systems and Methods for Implanting Tissue Stimulation Electrodes in the Pelvic Region
US20090012592A1 (en) * 2006-07-10 2009-01-08 Ams Research Corporation Tissue anchor
US8160710B2 (en) 2006-07-10 2012-04-17 Ams Research Corporation Systems and methods for implanting tissue stimulation electrodes in the pelvic region
US9333367B2 (en) 2006-07-28 2016-05-10 Boston Scientific Neuromodulation Corporation Charger with orthogonal PCB for implantable medical device
US20080027500A1 (en) * 2006-07-28 2008-01-31 Advanced Bionics Corporation Charger With Orthogonal PCB For Implantable Medical Device
US9002445B2 (en) 2006-07-28 2015-04-07 Boston Scientific Neuromodulation Corporation Charger with orthogonal PCB for implantable medical device
US7509175B2 (en) 2006-08-03 2009-03-24 Intrapace, Inc. Method and devices for stimulation of an organ with the use of a transectionally placed guide wire
US20080058876A1 (en) * 2006-09-06 2008-03-06 Giancarlo Barolat Implantable reel for coiling an implantable elongated member
US7769443B2 (en) 2006-09-06 2010-08-03 Giancarlo Barolat Implantable reel for coiling an implantable elongated member
US10456585B2 (en) 2006-10-26 2019-10-29 Boston Scientific Neuromodulation Corporation System and method to automatically maintain electrical stimulation intensity
US9943694B2 (en) 2006-10-26 2018-04-17 Boston Scientific Neuromodulation Corporation System and method to automatically maintain electrical stimulation intensity
US9352161B2 (en) 2006-10-26 2016-05-31 Boston Scientific Neuromodulation Corporation Method of maintaining intensity output while adjusting pulse width or amplitude
US20080103559A1 (en) * 2006-10-26 2008-05-01 Advanced Bionics Corporation Method of maintaining intensity output while adjusting pulse width or amplitude
US11439831B2 (en) 2006-10-26 2022-09-13 Boston Scientific Neuromodulation Corporation Automatic adjustment to maintain evoked potential feature
US10561835B2 (en) 2006-10-31 2020-02-18 Medtronic, Inc. Implantable medical lead with threaded fixation
US20080132970A1 (en) * 2006-12-05 2008-06-05 Giancarlo Barolat Method and system for treatment of intractable scrotal and/or testicular pain
US20080183224A1 (en) * 2007-01-25 2008-07-31 Giancarlo Barolat Electrode paddle for neurostimulation
US8554337B2 (en) 2007-01-25 2013-10-08 Giancarlo Barolat Electrode paddle for neurostimulation
US8594785B2 (en) 2007-02-01 2013-11-26 Boston Scientific Neuromodulation Corporation Neurostimulation system and method for measuring patient activity
US20080188909A1 (en) * 2007-02-01 2008-08-07 Boston Scientific Neuromodulation Corporation Neurostimulation system and method for measuring patient activity
US8549015B2 (en) 2007-05-01 2013-10-01 Giancarlo Barolat Method and system for distinguishing nociceptive pain from neuropathic pain
US7932696B2 (en) 2007-05-14 2011-04-26 Boston Scientific Neuromodulation Corporation Charger alignment indicator with adjustable threshold
US8044635B2 (en) 2007-05-14 2011-10-25 Boston Scientific Neuromodulation Corporation Charger alignment indicator with adjustable threshold
US8598841B2 (en) 2007-05-14 2013-12-03 Boston Scientific Neuromodulation Corporation Charger alignment indicator with adjustable threshold
EP2495015A1 (en) 2007-05-14 2012-09-05 Boston Scientific Neuromodulation Corporation Smart charger alignment indicator
US20110172742A1 (en) * 2007-05-14 2011-07-14 Boston Scientific Neuromodulation Corporation Smart charger alignment indicator
WO2008142402A1 (en) 2007-05-22 2008-11-27 Ivor Stephen Gillbe Array stimulator
US8612018B2 (en) 2007-05-22 2013-12-17 Ivor Stephen Gillbe Array stimulator
US20100049289A1 (en) * 2007-07-10 2010-02-25 Ams Research Corporation Tissue anchor
US8774942B2 (en) 2007-07-10 2014-07-08 Ams Research Corporation Tissue anchor
US9427573B2 (en) 2007-07-10 2016-08-30 Astora Women's Health, Llc Deployable electrode lead anchor
US20090099439A1 (en) * 2007-10-16 2009-04-16 Giancarlo Barolat Surgically implantable electrodes
US8214057B2 (en) 2007-10-16 2012-07-03 Giancarlo Barolat Surgically implantable electrodes
US8185207B2 (en) 2007-10-26 2012-05-22 Medtronic, Inc. Medical device configuration based on sensed brain signals
US7983757B2 (en) 2007-10-26 2011-07-19 Medtronic, Inc. Medical device configuration based on sensed brain signals
US20090112281A1 (en) * 2007-10-26 2009-04-30 Medtronic, Inc. Medical device configuration based on sensed brain signals
US9289610B2 (en) 2008-05-15 2016-03-22 Boston Scientific Neuromodulation Corporation Fractionalized stimulation pulses in an implantable stimulator device
US9782593B2 (en) 2008-05-15 2017-10-10 Boston Scientific Neuromodulation Corporation Fractionalized stimulation pulses in an implantable stimulator device
US20090287279A1 (en) * 2008-05-15 2009-11-19 Boston Scientific Neuromodulation Corporation Current steering for an implantable stimulator device involving fractionalized stimulation pulses
US10293166B2 (en) 2008-05-15 2019-05-21 Boston Scientific Neuromodulation Corporation Fractionalized stimulation pulses in an implantable stimulator device
US20100262210A1 (en) * 2008-05-15 2010-10-14 Boston Scientific Neuromodulation Corporation Current Steering for an Implantable Stimulator Device Involving Fractionalized Stimulation Pulses
US8812131B2 (en) 2008-05-15 2014-08-19 Boston Scientific Neuromodulation Corporation Current steering for an implantable stimulator device involving fractionalized stimulation pulses
US7890182B2 (en) 2008-05-15 2011-02-15 Boston Scientific Neuromodulation Corporation Current steering for an implantable stimulator device involving fractionalized stimulation pulses
US9393423B2 (en) 2008-05-15 2016-07-19 Boston Scientific Neuromodulation Corporation Fractionalized stimulation pulses in an implantable stimulator device
US20100010582A1 (en) * 2008-07-11 2010-01-14 Boston Scientific Neuromodulation Corporation Medical system and method for setting programmable heat limits
US8055337B2 (en) 2008-07-24 2011-11-08 Boston Scientific Neuromodulation Corporation System and method for maintaining a distribution of currents in an electrode array using independent voltage sources
US20100023070A1 (en) * 2008-07-24 2010-01-28 Boston Scientific Neuromodulation Corporation System and method for maintaining a distribution of currents in an electrode array using independent voltage sources
US8131358B2 (en) 2008-07-24 2012-03-06 Boston Scientific Neuromodulation Corporation System and method for maintaining a distribution of currents in an electrode array using independent voltage sources
US20100023069A1 (en) * 2008-07-24 2010-01-28 Boston Scientific Neuromodulation Corporation System and method for maintaining a distribution of currents in an electrode array using independent voltage sources
US20100087706A1 (en) * 2008-09-30 2010-04-08 Intrapace, Inc. Lead Access
US10737103B2 (en) 2008-12-03 2020-08-11 Boston Scientific Neuromodulation Corporation External charger with adjustable alignment indicator
US20100137948A1 (en) * 2008-12-03 2010-06-03 Boston Scientific Neuromodulation Corporation External charger with adjustable alignment indicator
US9227075B2 (en) 2008-12-03 2016-01-05 Boston Scientific Neuromodulation Corporation External charger with adjustable alignment indicator
US10010717B2 (en) 2008-12-03 2018-07-03 Boston Scientific Neuromodulation Corporation External charger with adjustable alignment indicator
US9403013B2 (en) 2009-01-29 2016-08-02 Nevro Corporation Systems and methods for producing asynchronous neural responses to treat pain and/or other patient conditions
US8255057B2 (en) 2009-01-29 2012-08-28 Nevro Corporation Systems and methods for producing asynchronous neural responses to treat pain and/or other patient conditions
US10173065B2 (en) 2009-01-29 2019-01-08 Nevro Corp. Systems and methods for producing asynchronous neural responses to treat pain and/or other patient conditions
US10918867B2 (en) 2009-01-29 2021-02-16 Nevro Corp. Systems and methods for producing asynchronous neural responses to treat pain and/or other patient conditions
US10179241B2 (en) 2009-01-29 2019-01-15 Nevro Corp. Systems and methods for producing asynchronous neural responses to treat pain and/or other patient conditions
US11883670B2 (en) 2009-01-29 2024-01-30 Nevro Corp. Systems and methods for producing asynchronous neural responses to treat pain and/or other patient conditions
US8849410B2 (en) 2009-01-29 2014-09-30 Nevro Corporation Systems and methods for producing asynchronous neural responses to treat pain and/or other patient conditions
US8509906B2 (en) 2009-01-29 2013-08-13 Nevro Corporation Systems and methods for producing asynchronous neural responses to treat pain and/or other patient conditions
US20110046660A1 (en) * 2009-02-13 2011-02-24 Intrapace, Inc. Endoscopic Forceps With Removable Handle
US20100217340A1 (en) * 2009-02-23 2010-08-26 Ams Research Corporation Implantable Medical Device Connector System
US9539433B1 (en) 2009-03-18 2017-01-10 Astora Women's Health, Llc Electrode implantation in a pelvic floor muscular structure
US20110087076A1 (en) * 2009-04-03 2011-04-14 Intrapace, Inc. Feedback systems and methods for communicating diagnostic and/or treatment signals to enhance obesity treatments
US8715181B2 (en) 2009-04-03 2014-05-06 Intrapace, Inc. Feedback systems and methods for communicating diagnostic and/or treatment signals to enhance obesity treatments
US20110034760A1 (en) * 2009-04-03 2011-02-10 Intrapace, Inc. Feedback systems and methods to enhance obstructive and other obesity treatments
US20110160793A1 (en) * 2009-12-31 2011-06-30 Ams Research Corporation Multi-Zone Stimulation Implant System and Method
US8380312B2 (en) 2009-12-31 2013-02-19 Ams Research Corporation Multi-zone stimulation implant system and method
US20110298304A1 (en) * 2010-06-07 2011-12-08 Thoratec Corporation Bi-ventricular percutaneous cable
US8668526B2 (en) 2010-06-07 2014-03-11 Thoratec Corporation Bi-ventricular percutaneous cable
US8388384B2 (en) * 2010-06-07 2013-03-05 Thoratec Corporation Bi-ventricular percutaneous cable
US9220887B2 (en) 2011-06-09 2015-12-29 Astora Women's Health LLC Electrode lead including a deployable tissue anchor
US9731112B2 (en) 2011-09-08 2017-08-15 Paul J. Gindele Implantable electrode assembly
US9728981B2 (en) 2012-08-31 2017-08-08 Alfred E. Mann Foundation For Scientific Research Feedback controlled coil driver for inductive power transfer
US9682237B2 (en) 2013-03-15 2017-06-20 Alfred E. Mann Foundation For Scientific Research High voltage monitoring successive approximation analog to digital converter
US10603495B2 (en) 2013-03-15 2020-03-31 The Alfred E. Mann Foundation For Scientific Research Current sensing multiple output current stimulators
US9981130B2 (en) 2013-03-15 2018-05-29 Alfred E. Mann Foundation For Scientific Research Current sensing multiple output current stimulators
US11338144B2 (en) 2013-03-15 2022-05-24 Alfred E. Mann Foundation For Scientific Research Current sensing multiple output current stimulators
US9446241B2 (en) 2013-03-15 2016-09-20 Alfred E. Mann Foundation For Scientific Research Current sensing multiple output current stimulators
US10029090B2 (en) 2013-05-03 2018-07-24 Alfred E. Mann Foundation For Scientific Research Multi-branch stimulation electrode for subcutaneous field stimulation
US9308378B2 (en) 2013-05-03 2016-04-12 Alfred E. Mann Foundation For Scientific Research Implant recharger handshaking system and method
US9675807B2 (en) 2013-05-03 2017-06-13 Alfred E. Mann Foundation For Scientific Research High reliability wire welding for implantable devices
US9789325B2 (en) 2013-05-03 2017-10-17 Alfred E. Mann Foundation For Scientific Research Implant recharger handshaking system and method
US9433779B2 (en) 2013-05-03 2016-09-06 Alfred E. Mann Foundation For Scientific Research Multi-branch stimulation electrode for subcutaneous field stimulation
US11722007B2 (en) 2013-07-29 2023-08-08 The Alfred E. Mann Foundation For Scientific Rsrch Microprocessor controlled class E driver
US10971950B2 (en) 2013-07-29 2021-04-06 The Alfred E. Mann Foundation For Scientific Research Microprocessor controlled class E driver
US9855436B2 (en) 2013-07-29 2018-01-02 Alfred E. Mann Foundation For Scientific Research High efficiency magnetic link for implantable devices
US9780596B2 (en) 2013-07-29 2017-10-03 Alfred E. Mann Foundation For Scientific Research Microprocessor controlled class E driver
US10449377B2 (en) 2013-07-29 2019-10-22 The Alfred E. Mann Foundation For Scientific Research High efficiency magnetic link for implantable devices
US10447083B2 (en) 2013-07-29 2019-10-15 The Alfred E. Mann Foundation For Scientific Research Microprocessor controlled class E driver
US10384055B2 (en) 2013-12-04 2019-08-20 Boston Scientific Neuromodulation Corporation Insertion tool for implanting a paddle lead and methods and systems utilizing the tool
US9867981B2 (en) 2013-12-04 2018-01-16 Boston Scientific Neuromodulation Corporation Insertion tool for implanting a paddle lead and methods and systems utilizing the tool
US11389659B2 (en) 2014-08-15 2022-07-19 Axonics, Inc. External pulse generator device and associated methods for trial nerve stimulation
US11116985B2 (en) 2014-08-15 2021-09-14 Axonics, Inc. Clinician programmer for use with an implantable neurostimulation lead
US10406369B2 (en) 2014-08-15 2019-09-10 Axonics Modulation Technologies, Inc. Electromyographic lead positioning and stimulation titration in a nerve stimulation system for treatment of overactive bladder
US11730411B2 (en) 2014-08-15 2023-08-22 Axonics, Inc. Methods for determining neurostimulation electrode configurations based on neural localization
US9855423B2 (en) 2014-08-15 2018-01-02 Axonics Modulation Technologies, Inc. Systems and methods for neurostimulation electrode configurations based on neural localization
US9700731B2 (en) 2014-08-15 2017-07-11 Axonics Modulation Technologies, Inc. Antenna and methods of use for an implantable nerve stimulator
US10478619B2 (en) 2014-08-15 2019-11-19 Axonics Modulation Technologies, Inc. Implantable lead affixation structure for nerve stimulation to alleviate bladder dysfunction and other indication
US11497916B2 (en) 2014-08-15 2022-11-15 Axonics, Inc. Electromyographic lead positioning and stimulation titration in a nerve stimulation system for treatment of overactive bladder
US9561372B2 (en) 2014-08-15 2017-02-07 Axonics Modulation Technologies, Inc. Electromyographic lead positioning and stimulation titration in a nerve stimulation system for treatment of overactive bladder
US10589103B2 (en) 2014-08-15 2020-03-17 Axonics Modulation Technologies, Inc. External pulse generator device and associated methods for trial nerve stimulation
US9427574B2 (en) 2014-08-15 2016-08-30 Axonics Modulation Technologies, Inc. Implantable lead affixation structure for nerve stimulation to alleviate bladder dysfunction and other indication
US9802038B2 (en) 2014-08-15 2017-10-31 Axonics Modulation Technologies, Inc. Implantable lead affixation structure for nerve stimulation to alleviate bladder dysfunction and other indication
US10682521B2 (en) 2014-08-15 2020-06-16 Axonics Modulation Technologies, Inc. Attachment devices and associated methods of use with a nerve stimulation charging device
US11213675B2 (en) 2014-08-15 2022-01-04 Axonics, Inc. Implantable lead affixation structure for nerve stimulation to alleviate bladder dysfunction and other indication
US10729903B2 (en) 2014-08-15 2020-08-04 Axonics Modulation Technologies, Inc. Methods for determining neurostimulation electrode configurations based on neural localization
US9555246B2 (en) 2014-08-15 2017-01-31 Axonics Modulation Technologies, Inc. Electromyographic lead positioning and stimulation titration in a nerve stimulation system for treatment of overactive bladder
US9533155B2 (en) 2014-08-15 2017-01-03 Axonics Modulation Technologies, Inc. Methods for determining neurostimulation electrode configurations based on neural localization
US9802051B2 (en) 2014-08-15 2017-10-31 Axonics Modulation Technologies, Inc. External pulse generator device and associated methods for trial nerve stimulation
US10092762B2 (en) 2014-08-15 2018-10-09 Axonics Modulation Technologies, Inc. Integrated electromyographic clinician programmer for use with an implantable neurostimulator
US9895546B2 (en) 2015-01-09 2018-02-20 Axonics Modulation Technologies, Inc. Patient remote and associated methods of use with a nerve stimulation system
US9770596B2 (en) 2015-01-09 2017-09-26 Axonics Modulation Technologies, Inc. Antenna and methods of use for an implantable nerve stimulator
US11484723B2 (en) 2015-01-09 2022-11-01 Axonics, Inc. Attachment devices and associated methods of use with a nerve stimulation charging device
US11478648B2 (en) 2015-01-09 2022-10-25 Axonics, Inc. Antenna and methods of use for an implantable nerve stimulator
US10384067B2 (en) 2015-01-09 2019-08-20 Axonics Modulation Technologies, Inc. Patient remote and associated methods of use with a nerve stimulation system
US11123569B2 (en) 2015-01-09 2021-09-21 Axonics, Inc. Patient remote and associated methods of use with a nerve stimulation system
US10722721B2 (en) 2015-01-09 2020-07-28 Axonics Modulation Technologies, Inc. Antenna and methods of use for an implantable nerve stimulator
US10105542B2 (en) 2015-01-09 2018-10-23 Axonics Modulation Technologies, Inc. Patient remote and associated methods of use with a nerve stimulation system
US9956000B2 (en) 2015-01-13 2018-05-01 Boston Scientific Neuromodulation Corporation Insertion tool for implanting a paddle lead and methods and systems utilizing the tool
US9925381B2 (en) 2015-07-10 2018-03-27 Axonics Modulation Technologies, Inc. Implantable nerve stimulator having internal electronics without ASIC and methods of use
US10850104B2 (en) 2015-07-10 2020-12-01 Axonics Modulation Technologies, Inc. Implantable nerve stimulator having internal electronics without ASIC and methods of use
US11766568B2 (en) 2015-07-10 2023-09-26 Axonics, Inc. Implantable nerve stimulator having internal electronics without ASIC and methods of use
US11318310B1 (en) 2015-10-26 2022-05-03 Nevro Corp. Neuromodulation for altering autonomic functions, and associated systems and methods
US10195423B2 (en) 2016-01-19 2019-02-05 Axonics Modulation Technologies, Inc. Multichannel clip device and methods of use
US9517338B1 (en) 2016-01-19 2016-12-13 Axonics Modulation Technologies, Inc. Multichannel clip device and methods of use
US11602638B2 (en) 2016-01-29 2023-03-14 Axonics, Inc. Methods and systems for frequency adjustment to optimize charging of implantable neurostimulator
US10603500B2 (en) 2016-01-29 2020-03-31 Axonics Modulation Technologies, Inc. Methods and systems for frequency adjustment to optimize charging of implantable neurostimulator
US11083903B2 (en) 2016-01-29 2021-08-10 Axonics, Inc. Methods and systems for frequency adjustment to optimize charging of implantable neurostimulator
US11260236B2 (en) 2016-02-12 2022-03-01 Axonics, Inc. External pulse generator device and affixation device for trial nerve stimulation and methods of use
US10376704B2 (en) 2016-02-12 2019-08-13 Axonics Modulation Technologies, Inc. External pulse generator device and associated methods for trial nerve stimulation
US11511122B2 (en) 2018-02-22 2022-11-29 Axonics, Inc. Neurostimulation leads for trial nerve stimulation and methods of use
US11110283B2 (en) 2018-02-22 2021-09-07 Axonics, Inc. Neurostimulation leads for trial nerve stimulation and methods of use
US11590352B2 (en) 2019-01-29 2023-02-28 Nevro Corp. Ramped therapeutic signals for modulating inhibitory interneurons, and associated systems and methods
US11642537B2 (en) 2019-03-11 2023-05-09 Axonics, Inc. Charging device with off-center coil
US11848090B2 (en) 2019-05-24 2023-12-19 Axonics, Inc. Trainer for a neurostimulator programmer and associated methods of use with a neurostimulation system
US11439829B2 (en) 2019-05-24 2022-09-13 Axonics, Inc. Clinician programmer methods and systems for maintaining target operating temperatures

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