Source: https://patents.justia.com/patent/10413721
Timestamp: 2019-10-18 06:36:40
Document Index: 192412695

Matched Legal Cases: ['Application No. 61', 'art 42', 'art 42', 'art 42', 'art 42', 'art 42', 'art 42', 'art 42', 'art 42', 'art 42', 'art 42', 'art 42', 'art 42', 'art 42', 'art 42', 'art 42', 'art 42', 'art 42', 'art 42', 'art 42']

US Patent for System and method for implantable medical device lead shielding Patent (Patent # 10,413,721 issued September 17, 2019) - Justia Patents Search
Justia Patents AnchoredUS Patent for System and method for implantable medical device lead shielding Patent (Patent # 10,413,721)
Aug 14, 2017 - MEDTRONIC, INC.
Multi-chamber intracardiac pacing system
Therapeutic window determination
This application claims the benefit of U.S. Provisional Application No. 61/035956, filed on Mar. 12, 2008. The disclosure of the above application is incorporated herein by reference.
Provided is an implantable medical device operable to provide a therapy to an anatomical structure. The device can include a therapy device implanted in a portion of the anatomical structure and operable to generate the therapy for the anatomical structure. The device can also include a lead having a proximal end, a distal end and a lead body that includes a first outer conductive braid, a second outer conductive braid and a multilumen member. The first outer conductive braid and the second outer conductive braid can be disposed about the multilumen member. The device can include a first electrode fixedly coupled between the proximal end and the distal end of the lead such that the first electrode is positioned adjacent to a first portion of the anatomical structure. The first electrode can be in communication with the first outer conductive braid and the second outer conductive braid. The device can also include a first inner conductor that can pass through a portion of the multilumen member. The first inner conductor can be in electrical communication with the first electrode to deliver a therapy to the first portion of the anatomical structure. The device can include a tip electrode extending beyond the distal end of the lead arid a tip inner conductor that can pass through a portion of the multilumen member. The tip inner conductor can be in electrical communication with the tip electrode to deliver a therapy to a second portion of the anatomical structure. The device can include a second electrode coupled adjacent to the tip electrode at the distal end of the lead such that the second electrode is positioned adjacent to a third portion of the anatomical structure. The device can further include a second inner conductor that can pass through a portion of the multilumen member. The second inner conductor can be in electrical communication with the second electrode to deliver a therapy to the third portion of the anatomical structure. The first outer conductive braid can be disposed between the proximal end of the lead and the first electrode, and the second outer conductive braid can be disposed between the first electrode and the second electrode. The first electrode can dissipate a current induced in the first outer conductive braid and second outer conductive braid, via the first portion of the anatomical structure.
Further provided is a method of forming a cardiac lead system for implantation into an anatomical structure. The method can include providing a lead having a multilumen member that can pass; through the lead, a first electrode in electrical communication with a first inner conductor and fixedly coupled to the multilumen member, the first inner conductor passing through a portion of the multilumen member, and a second electrode in electrical communication with a second inner conductor and extending beyond an end of the multilumen member, the second inner conductor passing through a portion of the multilumen member. The method can also include providing the first electrode with a first surface area and the second electrode with a second surface area, with the first surface area being larger than the second surface area. The method can include covering a substantial portion of the lead with a shield, and electrically coupling the shield to the first electrode.
With reference to FIG. 1, an implantable medical device (IMD) 20, which can include implantable pulse generator (IPG) devices, implantable cardioverter-defibrillator (ICD) devices, cardiac resynchronization therapy defibrillator devices, or combinations thereof, is exemplarily illustrated. The IMD 20 can include an implantable case or body assembly 22 The implantable case 22 can be formed of appropriate materials and include appropriate features, such as a hermetically sealed body wall 24. The body wall 24 can be made of a substantially inert material or of a conducting material.
Contained within or associated with the case 22 can be a power device 25 (i.e., battery), a controller assembly 26, and a connector body 27. The controller assembly 26 can include a circuit board having a processor, memory, transmitter, receiver, and other appropriation portions, further discussed herein. The connector body 27 can extend from or be integrated with the case 22. The connector body 27 can include multiple ports 28 that each interconnect with a connector terminal 30 of a lead assembly 32. FIG. 1 illustrates two lead assemblies 32a, 32b where each lead assembly 32a, 32b includes lead bodies 34a, 34b extending from tip electrodes 36a, 36b. Although the IMD 20 is illustrated in FIGS. 1 and 2 as including two lead assemblies 32a, 32b, it will be understood that any number of lead assemblies 32 could be employed with the IMD 20 depending upon the malady of the patient and the particular IMD 20 employed. Moreover, the switch assembly further discussed herein can be associated with one or all of the lead assemblies 32a, 32b for the particular IMD 20 employed.
A fixation mechanism can also be included with each lead assembly 32a, 32b to affix each tip electrode 36a, 36b relative to or in a selected tissue of the patient. The fixation mechanism can be near each tip electrode 36a, 36b or define a portion of the tip electrode 36a, 36b. Fixation mechanisms can be any appropriate type, including a grapple mechanism, a helical mechanism, a drug-coated connection mechanism, and other appropriate connection mechanisms.
A majority of each lead body 34a, 34b can also be formed in a generally known and selected manner. For example, the various conductors and electrical components can be encased in silicone, polyurethane, and other appropriate materials. For example, at least one inner conductor 136 (FIG. 5) can extend from each connector terminal 30 to engage each tip electrode 36a, 36b (identified as 132d in FIG. 4). It will be understood by one skilled in the art, the inner conductor 136 can be one piece or multiple components that are interconnected. Also, more than one conductor can be provided, such as one conductor for each electrode in each lead assembly 32a, 32b. The inner conductor 136 can also be cannulated or include a solid or non-cannulated cable. The casing material of each lead body 34a, 34b can electrically insulate the inner electrical conductor from an external environment.
The IMD 20, including the components discussed above; can be implanted in a patient 40 as illustrated in FIG. 2. The IMD 20 can include one or more lead assemblies 32, such as the first lead assembly 32a and the second lead assembly 32b. The first lead assembly 32a arid the second lead assembly 32b can be connected to the connector body 27. As one skilled in the art will understand, the position of lead bodies 34a, 34b can depend upon the type of IMD and the malady of the patient 40. For example, the lead assemblies 32a, 32b can be positioned transvenously to positions within a heart 42 or on the outside of the heart 42. The IMD 20 can be provided to pace the heart 42, defibrillate the heart 42, sense conditions of the heart 42, etc.
The IMD 20, including the case 22 and the lead bodies 34a, 34b, can be implanted using known procedures. For example, an incision can be made in a chest wall or an abdomen wall of the patient 40 and the lead assemblies 32a, 32b can be passed through selected veins to selected portions of the heart 42 of the patient 40. The case 22 can also be positioned through the incision into a chest wall or abdominal wall of the patient 40. In a selected procedure, the leads assemblies 32a, 32b can be passed through a superior vena cava 44 of the patient 40. The lead tips or tip electrodes 36a, 36b can be positioned at various positions in the heart 42, such as at the ventricles or atriums thereof. The position of the lead assemblies 32a, 32b and tip electrodes 36a, 36b can be selected for pacing, defibrillation, sensing, or other appropriate procedures. The specific implantation procedure, position of the tip electrodes 36a, 36b, and the like can depend upon the patient 40, the surgeon performing the procedure, the specifics of the lead assemblies 32a, 32b, or other considerations.
As discussed above, the IMD 20, including the case 22 and the lead assemblies 32a, 32b can include various features or controls to defibrillate or pace the heart 42. The controls can include a processor associated with the controller assembly 26 located within the case 22. The processor can be programmed to control driving a current through the lead bodies 34a, 34b to the tip electrodes 36a, 36b to defibrillate or pace the heart 42.
Moreover, the IMD 20, including the case 22 and the lead assemblies 32a, 32b, can be formed to counteract or interact with various environmental factors. For example, the lead assemblies 32a, 32b can include features or portions to re-direct or dissipate thermal energy created by an induced current. Induced currents can be created due to an external field, such as an electromagnetic field acting on the conductors of the lead assemblies 32a, 32b.
For example, according to various embodiments, the patient 40 which has the implanted IMD 20 may receive a certain therapy or diagnostic technique, such as a magnetic resonance image (MRI) scan. Although not illustrated, a MRI, generally understood by one skilled in the art, uses high frequency electromagnetic pulses and strong magnetic fields to create image data regarding the patient 40. Generally, a MRI will have a frequency of about 42 MHz per tesla. Many common MRI systems use about 1.5 tesla magnetic fields and have a corresponding RF frequency of about 63 MHz. Without being bound by the theory, the strong magnetic fields in a MRI can induce aligned spins of sub-atomic particles arid the high frequency RF pulses can be used to change the alignment or otherwise affect the sub-atomic particles within the patient 40.
The strong magnetic fields and electromagnetic pulses may induce currents within the lead assemblies 32a, 32b of the IMD 20. The current induced in the lead assemblies 32a, 32b may cause certain affects, including heating, of the various lead components. According to various embodiments, such as those discussed herein, components, controls and/or mechanisms can be provided to reduce or eliminate the amount of current or thermal energy induced within each tip electrode 36a, 36b, or increase an area over which the current or thermal energy can be; dissipated.
As will be discussed further herein, each electrode assembly 130 can include an electrode 132 and a transmission member 134, which includes an inner conductor 136 and an insulative member 138. Briefly, the electrode 132 can be in contact with the anatomical structure to deliver a therapy to the anatomical structure, such as an electrical pulse, and can be in communication with the inner conductor 136 to receive the therapy. Thus, the inner conductor 136 can be in electrical communication with the electrode 132 and the ICD 120 to receive the therapy. In this example, the lead 122 can include four electrode assemblies 130, labeled 130a, 130b, 130c, 130d from the proximal end 124 to the distal end 126 of the lead 122. It should be noted that while the lead 122 is illustrated with four electrode assemblies 130 in FIG. 3, the lead 122 may have any number of electrode assemblies 130.
The proximal end 124 of the lead 122 can include a connector portion 140. As the connector portion 140 can be generally known, the connector portion will not be discussed in great detail herein. Briefly, however, the connector portion 140 can electrically couple the lead 122 to the ICD 120. the distal end 126 can terminate within the anatomical structure adjacent to the desired location for the delivery of the therapy, and generally, for example, can terminate adjacent to an apex of the heart 42, such as the right ventricular apex A, a ventricle, such as the right ventricle 42a, or other chambers, such as the right atria 42b, of the heart 42. As will be discussed, one electrode 132 of the at least one electrode assembly 130 can be coupled to the distal end 126 to deliver a therapy to the atrium A of the heart 42.
The at least one conductive member 144 can comprise a first conductive braid 144a and a second conductive braid 144b. The at least one conductive member 144 can generally extend for a majority of a length of the lead 122, and can generally be electrically coupled to the electrode 132 positioned near a proximal end 124 of the lead 122. It will be understood that although the at least One conductive member 144 is illustrated arid described herein as comprising a braid, the at least one conductive member 144 could also comprise any desired shape or structure, such as a coil, continuous tubular structure, etc., and thus, need not be composed of a plurality of interwoven conductive members as shown. The first conductive braid 144a can extend from the proximal end 124 of the lead 122 to the electrode assembly 130 located near a proximal end of the electrode assembly 130a. The second conductive braid 144b can extend from a distal end of the electrode assembly 130a to a proximal end of a second electrode assembly 130b. The first conductive braid 144a and the second conductive braid 144b can each be in electrical communication with the electrode 132a of the first electrode assembly 130a to dissipate a current induced in the first conductive braid 144a and the second conductive braid 144b through the electrode 132a.
The multilumen member 146 can be disposed within the first conductive braid 144a and the second conductive braid 144b. The multilumen member 146 can define at least one channel 148 for receipt of each of the inner conductors 136 associated with the electrode assemblies 130. Generally, the multilumen member 146 can be composed of a biocompatible material, such as a biocompatible polymer, for example, a silicone rubber. The at least one channel 148 can receive each of the inner conductors 136 of the electrode assemblies 130, arid can serve as a conduit that guides each of the inner conductors 136 from the ICD 120 to the electrode 132 of the respective electrode assembly 130. With reference to FIG. 6, the multilumen member 146 can also include one or more apertures 149 that extend out of a sidewall of the multilumen member 146. The apertures 149 can enable the various electrode assemblies 130 to be electrically coupled to the inner conductors 136 passing through the multilumen member 146.
With reference to FIGS. 3-6, selected ones of the electrode assemblies 130 can be operable to deliver the therapy to the anatomical structure, and a selected one of the electrode assemblies 130 can be operable to sense electrical activity at a desired site in the anatomical structure. The electrode assemblies 130 can include a first electrode or first defibrillator electrode assembly 130a, a second electrode or second defibrillator electrode assembly 130b, a sense electrode or ring electrode assembly 130c and a tip electrode assembly 130d.
With reference to FIGS. 4-6, the first defibrillator electrode assembly 130a can be coupled to the body 128 such that the first defibrillator electrode assembly 130a can be disposed between the proximal end 124 and the distal end 126. The first defibrillator electrode assembly 130a can include the first defibrillator electrode 132a and transmission member 134a. Generally, the first defibrillator electrode assembly 130a can be coupled to the body 128 such that when the lead 122 is implanted within the anatomical structure, such as the heart 42, the first defibrillator electrode 132a can be adjacent to a first portion of the anatomical structure, such as the superior vena cava 44 (FIG. 3).
With reference to FIGS. 3 and 6, the first defibrillator electrode 132a can have a first diameter D1 and a first surface area (generally indicated as A1 in phantom). The first diameter D1 can be substantially equivalent to a diameter D of the overlay 142 so that when the first defibrillator electrode 132a is coupled to the body 128, a smooth transition exists between the first defibrillator electrode 132a and the body 128. The first surface area A1 can be larger than a surface area of the electrode 132d of the distalmost electrode assembly 130d; generally indicated as SA in phantom. Generally, the first surface area A1 can range from about 400 square millimeters to about 1000 square millimeters, and generally can range from about 750 square millimeters to about 850 square millimeters. As shown in FIG. 6, the first defibrillator electrode 132a can be coupled to the at least one conductive member 144, the multilumen member 146 of the body 128, and the transmission member 134a. The transmission member 134a can pass through one of the channels 148 of the multilumen member 146, and can be in communication with and responsive to the ICD 120 to transmit an electrical signal or charge to the first defibrillator electrode 132a. The transmission member 134a can include the inner conductor 136a that is encased by or coated with an insulative member 138a, such as a biocompatible polymer, for example, a fluoropolymer.
With reference to FIGS. 4 and 6, the first defibrillator electrode 132a can be coupled to and in communication with the first conductive braid 144a and the second conductive braid 144b (FIG. 6). Generally, the location of the first defibrillator electrode assembly 130a can be fixed relative to a length of the lead 122 between the proximal end 124 and the distal end 126. The first defibrillator electrode 132a can be coupled to the first conductive braid 144a and the second conductive braid 144b, via any suitable mechanism that enables electrical communication between the first defibrillator electrode 132a, the first conductive braid 144a and the second conductive braid 144b. These mechanisms can include welding, crimping, conductive adhesives, conductive fasteners, etc., as generally indicated by reference numeral 141 in FIG. 6.
Accordingly, if a current is induced in the first conductive braid 144a and/or second conductive braid 144b from an external electric field, such as that generated by an MRI, the current and heat generated by the induced current can flow from the first conductive braid 144a and/or second conductive braid 144b into the first defibrillator electrode 132a, which is grounded by the body. With reference to FIG. 3, as the first defibrillator electrode 132a is adjacent to the anatomical structure, such as the superior vena cava 44, and has a large surface area A1, the current can be dissipated by the first defibrillator electrode 132a into the anatomical structure. This can ensure that if a current is induced in the first conductive braid 144a and/or second conductive braid 144b, any induced current flows to the electrode assembly 130 that has the largest surface area, such as the first defibrillator electrode assembly 130a. In other words, the at least one outer conductive member or shield 144 shields and prevents currents from being induced in the inner conductors 136 which are surrounded by the at least one outer conductive member or shield 144, thereby preventing induced currents from flowing to a smaller surface electrode assembly 130, such as the tip electrode 132d.
With reference to FIG. 6, the first defibrillator electrode 132a can be coupled to the transmission member 134a disposed in the multilumen member 146 via a connection 150. The connection 150 can couple the first defibrillator electrode 132a to the inner conductor 136a to enable electrical communication between the inner conductor 136a and the first defibrillator electrode 132a, The connection 150 can include a first end 150a and a second end 150b. The first end 150a can be crimped to the inner conductor 136a of the transmission member 134a, while the second end 150b can be coupled to the first defibrillator electrode 132a, through welding, for example.
With reference to FIGS. 3 and 4, the second defibrillator electrode assembly 130b can be coupled to the body 128 such that the second defibrillator electrode assembly 130b can be disposed near the distal end 126 of the lead 122, between the first electrode assembly 130a and the ring electrode assembly 130c. Generally, the location of the second defibrillator electrode assembly 130b can be fixed relative to the length of the lead 122 between the proximal end 124 and the distal end 126. The second defibrillator electrode assembly 130b can include the second defibrillator electrode 132b and the transmission member 134b. Generally, the second defibrillator electrode assembly 130a can be coupled to the body 128 such that when the lead 122 is implanted within the anatomical structure, such as the heart 42, the second defibrillator electrode 132b cart be adjacent to a second portion of the anatomical structure, such as a right ventricle 42a of the heart 42 (FIG. 3).
With reference to FIG. 3, the second defibrillator electrode 132b can have a second diameter D2 and a second surface area (generally indicated as A2 in phantom). The second diameter D2 can be substantially equivalent to the diameter D of the overlay 142 so that when the second defibrillator electrode 132b is coupled to the body 128, a smooth transition exists between the second defibrillator electrode 132b and the body 128. The second surface area A2 can be larger than the surface area SA of the tip electrode assembly 130d, but can be smaller than the first surface area A1 of the first defibrillator electrode 132a. Generally, the second surface area A2 can range from about 300 square millimeters to about 800 square millimeters, and generally can range from about 500 square millimeters to about 650 square millimeters.
The second defibrillator electrode 132b can be adjacent to, but not in electrical communication with the at least one conductive member 144, and can be coupled to the multilumen member 146 of the body 128, and the transmission member 134b. As the second defibrillator electrode 132b can be adjacent to, but not in electrical communication with the second conductive braid 144b, this can ensure that if a current is induced in the second conductive braid 144b, the current is communicated to the first defibrillator electrode 132a, which has a larger surface area A1 to dissipate the current, and can dissipate the current in a generally non-critical area of the anatomical structure. The transmission member 134b can pass through one of the channels 148 of the multilumen member 146, and the inner conductor 136b can be in communication with and responsive to the ICD 120 to transmit an electrical signal or charge to the second defibrillator electrode 132b. The inner conductor 136b can be encased by or coated with the insulative member 138b, which can comprise a biocompatible polymer, for example a fluoropolymer,
The second defibrillator electrode 132b can be coupled to the inner conductor 136b disposed in the multilumen member 146 via a suitable connection, such as the connection 150 (not specifically shown). In this regard, if employed, the connection 150 can electrically couple the second defibrillator electrode 132b to the inner conductor 136b. As the connection 150 between the inner conductor 136b and the second defibrillator electrode 132b can be substantially similar to that discussed with regard to the first defibrillator electrode assembly 130a, the connection 150 will not be discussed with regard to the second defibrillator electrode assembly 130b.
reference to FIGS. 3 and 4, the sense electrode or ring electrode assembly 130c can be coupled to the body 128 such that the ring electrode assembly 130c can be disposed near the distal end 126, between the second electrode assembly 130b and the tip electrode assembly 130d. As the ring electrode assembly 130c can be generally known in the art, and can be similar to the ring electrode assembly of the SPRINT QUATTRO SECURE™ cardiac lead commercially available from Medtronic, Inc. of Minneapolis, Minn., the ring electrode assembly 130c will not be discussed in great detail herein. Briefly, however, the ring electrode assembly 130c can include a ring electrode 132c (FIG. 4) and a transmission member 134c (FIG. 5). The ring electrode 132c can be adjacent to the anatomical structure, such as the heart 42, to receive electrical signals indicative of the electrical activity of the heart 42. These electrical signals can be transmitted to the ICD 120 via the inner conductor 136c of the transmission member 134c. The transmission member 134c can be disposed in one of the channels 148 of the multilumen member 146.
With reference to FIGS. 3-5, the tip electrode assembly 130d can extend beyond the multilumen member 146, and can contact the anatomical structure at a distalmost part, such as the right ventricular apex A of the heart 42. As the tip electrode assembly 130d can be generally known in the art, and can be similar to the tip electrode of the SPRINT QUATTRO SECURE™ cardiac lead commercially available from Medtronic, Inc. of Minneapolis, Minn., the tip electrode assembly 130d will not be discussed in great detail herein. Briefly, however, the tip electrode assembly 130d can include a tip electrode 130d and the transmission member 134d. The inner conductor 136d can electrically couple the tip electrode 132d to the ICD 120 so that the tip electrode 132d can to receive electrical signals and deliver a therapy, such as a pacing therapy, to the distalmost part of the anatomical structure. As illustrated in FIG. 3, the surface area SA of the tip electrode 132d can be smaller than the first surface area A1 of the first defibrillator electrode 132a and the second surface area A2 of the second defibrillator electrode 132b, and can range from about 1 square millimeter (mm2) to about 8 square millimeters (mm2).
With reference to FIGS. 3-6, in order to assemble the lead 122, in an exemplary process, the transmission members 134 can be inserted into the multilumen member 146. Then, the connection 150 can be coupled to the respective inner conductors 136 to couple the inner conductors 136 to the respective electrodes 132 (FIG. 6). The first conductive braid 144a and the second conductive braid 144b can then be positioned over the multilumen member 146. Next, the overlay 142 can be formed on, applied or extruded onto the first conductive braid 144a and second conductive braid 144b. The first conductive braid 144a and second conductive braid 144b can then be coupled to the first defibrillator electrode 132a such that the first conductive braid 144a and second conductive braid 144b are in communication with the first defibrillator electrode 132a. In one embodiment, the outer conductive member 144 can be combined with the overlay 142 in a separate operation, such as a continuous extrusion process or a discrete assembly arid heating reflow operation.
With the lead 122 assembled, the lead 122 can be coupled to the ICD 120, and the lead 122 and ICD 120 can be implanted into the anatomical structure. Generally, the lead 122 can be implanted such that the first defibrillator electrode 132a is adjacent to the superior vena cava 44, the second defibrillator electrode 132b is within the right ventricle 42a, and the tip electrode 132d is adjacent to the right ventricular apex A of the heart 42 (FIG. 3). If the anatomical structure encounters an external field, such as that generated by an MRI, a current may be induced in the at least one outer conductive member 144, which can serve to protect or shield the inner conductors 136 from the induced current, and thereby prevent the transmission of the induced current to an electrode assembly with a small surface area, such as the tip electrode 132d.
In this regard, as the at least one outer conductive member 144 covers, surrounds or shields the inner conductors 136 of the electrode assemblies 130, the external field generated by the MRI can induce a current in the at least one outer conductive member 144, thereby protecting or shielding the inner conductors 136 from the effects of the external field. Further, as the at least one outer conductive member 144 is in communication with the first defibrillator electrode 132a, the current and heat induced in the at least one outer conductive member 144 can be dissipated by the first defibrillator electrode 132a into the anatomical structure, which can serve to as a ground for the at least one outer conductive member 144.
1. A method of forming a medical lead system for implantation into an anatomical structure comprising:
providing a lead having a multilumen member passing through the lead, a first electrode in electrical communication with a first inner conductor and fixedly coupled to the multilumen member in a fixed intermediate position between a proximal end and a distal end of the lead, the first inner conductor passing through a portion of the multilumen member, and a second electrode in electrical communication with a second inner conductor and extending beyond an end of the multilumen member in a distal position on the lead, the second inner conductor passing through a portion of the multilumen member, the fixed intermediate position of the first electrode being closer to a longitudinal midpoint of the lead than to the second electrode;
providing the first electrode with a first surface area and the second electrode with a second surface area, with the first surface area being larger than the second surface area;
covering a substantial portion of the lead with a shield; and
electrically coupling the shield to the first electrode.
providing the lead with a third electrode in electrical communication with a third inner conductor and fixedly coupled to the multilumen member, the third inner conductor passing through a portion of the multilumen member; and
providing the lead with a sensing electrode in electrical communication with a fourth inner conductor and fixedly coupled to the multilumen member, the fourth inner conductor passing through a portion of the multilumen member.
3. The method of claim 2, wherein covering a substantial portion of the lead with a shield further comprises:
covering the lead from a proximal end of the lead to the first electrode with a first conductive member that being in electrical communication with the first electrode; and
covering the lead from the first electrode to the third electrode with a second conductive member that being in electrical communication with the first electrode.
providing an implantable therapy device;
implanting the therapy device into the anatomical structure; and
coupling the therapy device to the medical lead system such that the therapy device being in electrical communication with the first inner conductor, second inner conductor, third inner conductor and fourth inner conductor.
providing a programmer operable to be in communication with the implantable therapy device; and
programming the implantable therapy device to deliver a therapy through the medical lead system with the programmer.
6. A method of forming a medical lead system for implantation into an anatomical structure comprising:
electrically coupling the shield to the first electrode by the shield directly abutting the first electrode.
7822484 October 26, 2010 Zhao
7853332 December 14, 2010 Olsen
7941226 May 10, 2011 Marshall
8825180 September 2, 2014 Bauer
9901731 February 27, 2018 Marshall
20090171421 July 2, 2009 Atalar
Patent number: 10413721
Patent Publication Number: 20170368335
Inventor: Mark T. Marshall (Forest Lake, MN)
Assistant Examiner: Elizabeth K So
Application Number: 15/676,279
Current U.S. Class: Anchored (600/375)
International Classification: A61N 1/00 (20060101); A61N 1/05 (20060101); A61N 1/04 (20060101); A61N 1/08 (20060101);