WO2007059386A2 - Intravascular medical device - Google Patents

Intravascular medical device Download PDF

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Publication number
WO2007059386A2
WO2007059386A2 PCT/US2006/060556 US2006060556W WO2007059386A2 WO 2007059386 A2 WO2007059386 A2 WO 2007059386A2 US 2006060556 W US2006060556 W US 2006060556W WO 2007059386 A2 WO2007059386 A2 WO 2007059386A2
Authority
WO
WIPO (PCT)
Prior art keywords
housing
tether
ivmd
lead
means
Prior art date
Application number
PCT/US2006/060556
Other languages
French (fr)
Other versions
WO2007059386A3 (en
Inventor
Charles L. Dennis
George J. Klein
Ursula Gebhardt
Kenneth M. Anderson
Glen C. Zillmer
Original Assignee
Medtronic, Inc.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority to US11/271,018 priority Critical
Priority to US11/271,018 priority patent/US7862591B2/en
Application filed by Medtronic, Inc. filed Critical Medtronic, Inc.
Priority to PCT/US2006/060556 priority patent/WO2007059386A2/en
Priority claimed from EP20060839719 external-priority patent/EP1971398B1/en
Publication of WO2007059386A2 publication Critical patent/WO2007059386A2/en
Publication of WO2007059386A3 publication Critical patent/WO2007059386A3/en

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Classifications

    • 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
    • A61N1/38Applying electric currents by contact electrodes alternating or intermittent currents for producing shock effects
    • A61N1/39Heart defibrillators
    • A61N1/3956Implantable devices for applying electric shocks to the heart, e.g. for cardioversion
    • A61N1/3962Implantable devices for applying electric shocks to the heart, e.g. for cardioversion in combination with another heart therapy
    • 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
    • A61N1/372Arrangements in connection with the implantation of stimulators
    • A61N1/375Constructional arrangements, e.g. casings
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00Electrotherapy; Circuits therefor
    • A61N1/02Details
    • A61N1/04Electrodes
    • A61N1/05Electrodes for implantation or insertion into the body, e.g. heart electrode
    • A61N1/056Transvascular endocardial electrode systems
    • A61N1/057Anchoring means; Means for fixing the head inside the heart
    • A61N1/0573Anchoring means; Means for fixing the head inside the heart chacterised by means penetrating the heart tissue, e.g. helix needle or hook
    • A61N1/0575Anchoring means; Means for fixing the head inside the heart chacterised by means penetrating the heart tissue, e.g. helix needle or hook with drug delivery
    • 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
    • A61N1/372Arrangements in connection with the implantation of stimulators
    • A61N1/37205Microstimulators, e.g. implantable through a cannula
    • 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
    • A61N1/372Arrangements in connection with the implantation of stimulators
    • A61N1/378Electrical supply
    • A61N1/3785Electrical supply generated by biological activity or substance, e.g. body movement
    • 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
    • A61N1/372Arrangements in connection with the implantation of stimulators
    • A61N1/378Electrical supply
    • A61N1/3787Electrical supply from an external energy source
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00Electrotherapy; Circuits therefor
    • A61N1/02Details
    • A61N1/04Electrodes
    • A61N1/05Electrodes for implantation or insertion into the body, e.g. heart electrode
    • A61N1/056Transvascular endocardial electrode systems
    • A61N1/057Anchoring means; Means for fixing the head inside the heart
    • A61N2001/0582Suture sleeves

Abstract

An implantable medical device is configured so that all of the major components including a housing and attached leads are disposed within the vasculature of a patient. A tether extends from the housing of the device to an implant location where the tether is secured to tissue outside of the vasculature. In this manner, an intravascular medical device may be implanted at a location remote from final placement, delivered via the vasculature and anchored at the initial entry point.

Description

INTRAVASCULAR MEDICAL DEVICE

BACKGROUND FIELD OF THE INVENTION

The present invention relates to medical devices and in particular, implantable medical devices-

DESCRIPTION OF THE RELATED ART Medical devices related to managing, treating and providing therapy for cardiac conditions have changed and improved dramatically since their inception. Cardiac pacing, as an example, originally required an. external pulse generator that itself required external power. While providing life sustaining therapy, patients were tethered Io the power source and of course, power failures could prove catastrophic- Portable, battery powered externa] pulse generators were developed and provided the patient with the ability to be ambulatory; however, the pulse generator had to be earned by the patient. Furthermore, pacing leads were exposed through the patient's tissue and extreme care had to be exercised to minimize the risk of infection or inadvertent withdrawal

Subsequently, fully implantable, battery powered pulse generators were provided ill a hermetically sealed housing. This housing was rather large and was typically implanted in the abdomen of the patient with leads extending to the heart. Hie size of such a device often made it rather uncomfortable and the implantation procedure was relatively invasive.

As technology improved, implantable medical devices (IMDs) have become continuously smaller, while offering increased longevity, reliability and many more features and therapies. Epicardial leads that were attached to an externa! wall of the heart were replaced with endocardial leads that are implanted transvenously, thus becoming minimally invasive. With these smaller devices, the housing was no longer placed in the abdomen but instead was implanted subcuianeously or sub-rmiseuiarly, often m the pectoral region, A "pocket* is formed underneath the skin or muscle sufficiently large to receive the housing of the MD. The exposed or proximal ends of the leads are then connected to the housing and the incision is closed. While now routine, this is still a surgical procedure that .requires skill and the appropriate medical facilities.

In general, patients are comfortable with these implanted devices and have a full range of motion, without interference or hindrance. Some patients feel the housing in the "pocket," which may be physically and/or psychologically uncomfortable. Physically, some patients may press against the housing during certain physical activities making the housing noticeable. Even if not a hindrance or painful, simply "feeling" the presence of the device may remind that patient that they have a medical implant and/or medical condition aid this alone may he troubling to that patient. Some patients develop a hah.it of pressing against the pocket and hence against the IMD and often rotating or twisting the

IMD. Typically, IMDs that have one or more leads will have any excess lead length coiled under (or around) the housing of the ΪMD. Thus, frequent patient manipulation may cause portions of the 1ead(s) to twist or rub, potentially damaging the lead body or pulling the lead out of contact with the targeted tissue. This is sometimes referred to as "twiddlers syndrome."

As the size and capability of IMDs has greatly improved, use of these devices has naturally expanded. This results in greater knowledge and acceptance among the patient population as well as within the medical community. As a result, caregivers are using IMDs with more frequency and for new and diverse purposes. For example, pacemakers are used in patients with various bradyarrhythvnias. In such a patient, the heart's intrinsic pacing function fails or is deficient and the IMD provides electrical stimulation to maintain the proper heart rhythm. Such therapy is well known and is referred to above with the early, external pulse generators. Recently, the medical community has been using pacing technology in patient's whose heart rhythm k actually normal. Heart failure patients often have normal rhythm and conduction; however, this disease causes the heart to enlarge, As a result the left and right ventricles are xmsynchromxed when they contract even though the depolarization waveform triggering such a contraction was "timed" properly. Using cardiac ^synchronization therapy (CRT), the left and right ventricles are paced, leading to a mechanical 'Yesynchroriixation" of the left and right ventricular contractions. This not only leads to better immediate hemodynamic performance, but the heart itself often remodels itself {reducing in size) leading to an improvement in the disease state. Not only are new therapies and treatments developing, implantable devices are now being used to collect sensor data for a variety of purposes, For example, implantable loop recorders 0LRs) are implanted subeutanβously and record cardiac data. unobtrusively, for extended periods of time. This allows robust medical data to be collected that as a practical matter, may be otherwise unattainable.

These are .merely two examples that illustrate the ever increasing trend to beneficially me implantable .medical devices with greater frequency and for a wide variety of purposes that extend well beyond cardiac care. This presents a challenge to some caregivers who might want to use a given device for their patient but do not have ihe necessary surgical qualifications to actually implant the device. While such a patient may always be referred to another doctor, this adds cost and burden, some patients may not fellow through, aad some caregivers may simply opt for other treatments in order to maintain their relationship with the patient

BRIEF DESCRIPTION OF THE DRAWINGS

FKi 1 is a schematic illustration of selected internal components of an intravascular medical device (IVMD) consistent with the teachings of the present invention.

FiO, 2 is a schematic illustration of the IVMD including a teller and a lead FiG. 3 illustrates an electrode .incorporated into the tether,

FiG. 4 illustrates m JVMD having multiple leads, FiG. 5 is a sectional view of a housing of the IVMD. FIGS. 6 A - 6B illustrate an IVMD having a lead and the tether coupled to a common end of the housing. FIOS. 7A - 7B illustrate a system for deploying the lead. and. housing.

FIGS. 8A - SD illustrate an IVMD having a tether with a lumen. FiGS. 9A - 9D illustrate an IVMD having a tether with a lumen coaxial with a lumen through the housing and an attached lead. FIGS. 9E - H illustrate multiple lumens. FIG. 10 illustrates a housing having multiple housing portions.

FIGS, HA- HB illustrate multiple housing components with a common tether. FIGS. 12A - 12D illustrate a mechanism to attach a stylet to a housing component. FIGS. 13a 13b illustrate an IVMD with multiple housing portions, FIG-. 1.4 illustrates an IVMD having multiple .housing potions and multiple tethers. FIG. 1.5 illustrates an interaction of a stylet with both tethers of FlG. .14. FIG. 16 illustrates an IVMD with multiple housing portions. FIG. .17 illustrates an implanted IVMD.

FlG. .18 illustrates the anatomical relationship between the subclavian vein and the clavicle.

FIG. 19 illustrates the anatomical location of the cephalic vein. FIG-. 20 illustrates an IVMD implanted in lhe superior λ^ena cava having an auxiliary support member further anchoring the lead.

FlG. 21 A - 211 illustrate the insertion and anchoring of an IVMD.

FIGS. 22A - 22B illustrate a tether anchor.

FlG. 23 is a .flowchart: describing a process for implanting an IVMD.

DETAILED DESCRIPTION

FIG. 1 illustrates mi exemplary intravascular medical device (IVMD) 10. The IVMD 10 is an. implantable medical device that includes a hermetically sealed housing 12 containing components 18 to control, power, and operate the device. The housing 12 is shaped and configured to reside entirely within the vasculature anatomy or within a given organ (e.g.. the heart, lungs, kidney,, pancreas, etc.) via the vasculature. In one embodiment, the. housing 12 has art approximate diameter of 6-7 French. The IVMD 10 may have any number of functional areas including sensing, diagnostic, communications and therapy delivery. In the illustrated example, the IVMD 10 includes cardiac sensing- pacing and defibrillation as well as the ability to communicate- with an external device through telemetry.

The housing 12 includes a proximal header 16 and a distal header 16. The operative components .18 include a power source 20, such as a battery. One or more capacitors 22 are provided that allow charge to he accumulated for rapid discharge to deliver a defibrillation or cardioversion pulse. A pulse generator 26 is coupled to lhe power source 20 and provides electrical stimuli for cardiac pacing.

A microprocessor 24, memory 36 (.flash, EEPROM, ROM, RAM5 DRAM, harddisk. etc.), analog to digital converter (A/D) 30. analog signal processor 28, and digital signal processor (DSP) 32 are positioned within the bousing 12. An externally actuated switch 42 Is provided and may take the form of a reed switch that is closed by a magnet, Such a switch 42 may be used Io initiate a telemetry session with IVMD H). Alternatively., communication, may be initiated directly by an RF signal or other appropriate transmission medium. A telemetry module 34 provides the ability to transmit and receive data A reservoir 35 is optionally included. The reservoir may provide a supply of a deliverable drug (e.g., insulin), genetic material, or biologic. The ΪVMD 10 may provide for the release of the material on a given schedule or based upon sensed need. Some materials, such as insulin, may be dispersed as .needed but are predictably used; that is, the likelihood of delivery over a given time period is high. Other material may be delivered on an acute basis. For example, a dose of a blood thinner, coagulant, anticoagulant, or adrenaline is provided and released when necessitated.

An accelerometer 40 may be utilized to provide an indication of patient activity for a rate response function and/or a relative position indicator; that is. physical position of the patient (e.g., prone), finally, a sensor array 50 is illustrated. The sensor array 50 may sense any number of parameters such as temperature, pressure, velocity or other fluid flow characteristics, impedance, motion or size (e.g.. ultrasound for wail motion and/or chamber size), oxygenation, glucose, or the level of any sensed chemical substance. It should be appreciated that vvhϊie illustrated as contained within the housing 12, the sensor array 50 may have appropriate external portions not shown. For example, if used as a pressure sensor, a transducing membrane will form a part of housing 12 or part of a lead coupled with the housing 12, either physically or through telemetric connection (e.g., a body bus). Likewise, any additional componem(s) for sensor array 50 will be included in this manner, as required. Cardiac data (e.g., electrogram (EGM)) will be sensed via one or more leads as explained below- ϊ.n addition, the bousing J 2 may include one or more electrodes incorporated into the structure of the housing 12 (i.e., an active "can").

As indicated the power source 20 may be a single use battery . Alternatively, the battery may be rechargeable. As such, an optional recharging module 25 is illustrated. The recharging module 25 may receive power from an external source, such as directed RF energy, which is converted and used to recharge the battery 20. The RF energy may be collected via one or more antenna as discussed below, by using the housing 12 as an antenna, or by incorporating a receiver into the housing 12. Alternatively* or in addition. the rechargmg module 25 may use other mechanisms to generate power. In one embodiment, beat from within the patient is converted into current. In another embodiment, chemical energy from cells proximate fee implant location is co.overt.ed into electrical energy by the charging module 25. The charging module 25 may convert body motion into electrical energy. Such motion may come from multiple sources including without limitation gross patient mov ement {walking, exercising., etc.). lung motion (breathing), cardiac contractions, vasculature contraction (piilsitile blood flow), or fluid Sow, "Hie length of the unit provides the ability to harness mechanical power at one or more flexation points. Such flexation points may occur along the tether and/or in-between housing components. In this context, mechanical motion fa converted into electrical energy by various mechanisms such as movement of a magnetic member within a coil, lite charging module 25 may also used photovoltaic conversion to generate electrical current A .light collected placed sufficiently close to the surface of the patient's tissue will receive enough ambient light to provide power. Various other techniques are available to recharge the batten' and are considered to he within the spirit and scope of the present invention. The following documents are herein incorporated by reference in their entirety: US Patent 6,242,827. issued to Wolf et aϊ. on June 5r 2001 ; US Patent 6,768,246, issued to Pehioe et at on July 27, 2004; US Published Application 2004/0073267, published on April 15, 2004; and US Published Application 2004/0158294 published on August 12, 2004.

Tne module 25 has been described in conjunction with a traditional rechargeable baitery 20 as a raechaπ.is.m to recharge that battery. Ii should be appreciated, that to conserve space, the traditional battery 20 may be eliminated or greatly reduced in size (due to a decrease in reliance upon the battery). That is, the various mechanisms described to generate electrical energy from sources around the JVMD 10 may be used to directly power the IVMD 1 ϋ, without first storing that energy in a battery. This concept is applicable to any of the various forms the IVMD 10. Ja one embodiment providing power directly from module 23 is utilized when the IVMD has low or minimal power consumption requirements (e.g., periodic sensing). Thus, power is generated for internal operations and when communication is desired, external power Is provided for e.g., telemetry functions, through inductive coupling or RF power transmission. Of course, the IVMD 10 may be completely dependant upon such power conversion for all of its functionaEty, Finally, as indicated a smaller battery or capacϋor may be provided to collect some amount of energy prior to use; either to mitigate against fluctuation in the source (e.g.. movement stops for a period of time) or to provide an even power supply to mitigate against power fluctuations; that is, to provide a. relatively stable DC source. FiO. 2 illustrates a lead 60 coupled with the distal header 16. One or more electrodes are incorporated into the lead 60. As illustrated, lead 60 includes a helical affixation, member 64 that allows penetration, into tissue to secure the distal portion of the lead 60 at a specific site. The helical affixation member 64 may serve as an electrode and/or the distal end of the lead 60, proximal to the helical, member 64, acts as an electrode, A. coil electrode 62 is positioned proximal to the distal md of the lead 60 so that when implanted, the coil electrode creates a defibrillation vector through an appropriate cardiac path with another electrode of the ΪVMD 10. The length of the lead 60 and the relative position of the electrodes are selected based upon the type of therapies., sensing and diagnostics provided and. the implant location of the housing 12. The lead 60 may have other functions instead of or in addition to electrical stimulation or sensing. For example, a number of noa-electricai parameters (e,g.. pressure, temperature, velocity, chemical presence/concentration., etc.) may be sensed by providing an appropriate sensor. Hie lead 60 may haxfe a delivery device to deliver drugs, genetic .material, or biologies from the reservoir 35. Such a delivery device may include a needle 65a for delivery into tissue; a disbursing tip 65b (e.g., a porous surface for release into a fluid supply or against a larger surface area); or s variety of other deliver)- mechanisms. The lead 60 is connected to the distal header 16. The connection may be a permanent, integral formation. That is, the lead 60 and housing 12 are fabricated to form an integral unit or the lead 60 is permanently affixed to the housing 12. Alternatively,, the lead 60 is separable from the housing 12. as explained, below. As used throughout, the designations proximal and distal header 14, 16 are used to indicate particular portions of the housing 12. ϊt should be appreciated, that these portions may include a header in the traditional sense of an implantable medical device. That is, a separate portion from the remainder of the housing (hat includes various connection mechanisms (e.g., for receiving a. lead connector pin). Alternatively; the terminology- may simply refer to a given end or portion of the housing 12 to facilitate description. A flexible tether 70 extends from and k securely coupled to the proximal header 14, At a proximal end 74. the tether 70 has an anchoring point. In the illustrated embodiment, a T-shaped anchor member 76 is attached to the tether 70 at the anchoring point The anchor member 76 includes one or more suture ports 78 extending through the member 76. As indicated, ΪVMD 10 is implanted trsnsvenously and the entire housing 12 resides within the vasculature or within an organ accessed via the vasculature. The tether 70 extends .from the implanted location of the housing 12t through the vasculature and is anchored at or near the vasculature incision or puncture created for implantation. Thus, the tether 70 will fiiHy or partially maintain the position of the IVMD .! 0. For example, if implanted in the superior vena cava, with a pacing lead 60 extending from the housing 12 into a cardiac chamber, blood flow and gravity (generally) will provide force against the housing 12 ia a direction towards the heart. With the anchor point fixed, the housing 12 is prevented from traveling towards the heart and is thus secured. While suturing has been discussed, other methods of attaching or anchoring the tether 70 and/or the anchor 76.may be utilized

Hie anchoring point 74 allows for subsequent identification and access to the ΪVMD 10. That is, if the IVMD is replaced or modified, the anchoring point 74 is located and the IVMD 10 can be accessed or removed via the tether 70 along the same vasculature pathway, As such, the anchoring point 74 may optionally include s radiopaque marker, may be constructed of a biocompatible metal,, or having other identifying mechanisms to aid in determining the location of the anchor point 74 at a later time via X-ray s MRL or other imaging techniques. Alternatively, the anchor point 74 may be positioned sufficiently close to the surface of the patienf s skin that its location may he felt by applying pressure to the area The tether 70 is intended to secure the position of the ΪVMD 10 during the life of the implant Accordingly, the tether material is constructed of a suitably strong, flexible, biocompatible material. The length of the tether 70 may include a drug eiuting surface along the entire exterior, a portion of the exterior, or multiple distinct drug eiuting surfaces may be provided. In some embodiments, the tether 70 may be used to temporarily secure the I VMD 10 until another anchoring mechanism is enacted (e.g., fibrotic growth). In yet another alternative embodiment, the ΪVMD 10 is intended to degrade wilhin the body or pass harmlessly out of the body. For example, IVMD 10 may be a chemical sensor and the tether 70 secures the IVMD ! O at mi appropriate location within the vasculature, counteracting the forces of pulsitil.e blood flow. Eventually, the sensor will dissolve and in such an embodiment, the tether 70 could likewise dissolve. Of course, the tether 70 provides a convenient mechanism to remove any such device thus providing for temporary implantation of a variety of medical devices, including pacemakers aid defibrillators.

The tether 70 is provided with an excess length. After implantation of the lead 60 and housing 12, the desired length of tether 70 is determined. This final length should include enough excess to allow for normal movement of the housing .12 within the vasculature as well as any variations that will occur due to patient movement, positioning, growth or other physiological variations. The tether 70 is then cut at the appropriate location and anchored into place. The T-shaped anchor member 76, if used, is attached to the cut tether 70, either by suturing, mechanically clamping or using any other secure coupling mechanism. As indicated, excess tether length is provided at the proximal end of the tether 70 with an expectation that this excess will trimmed or remain unused. This allows for .flexibility during implantation aid minimizes the need to have multiple pre-configured devices to accommodate different patient sizes and implant locations. Conversely, a distal portion of the tether 70 will reliably remain intact. Thus, this portion of the tether 70 may be used to provide additional structure or functionality.

As illustrated in FIG. 2, an antenna 72 extends from the housing .12 and may be contained within or affixed to an miter portion, of the tether 70. Including the antenna 72 within the tether 70 provides ahermitic enclosure for the antenna 72 and any exposed ieedihroυgh. The length, ske. shape and configuration of the antenna 72 may vary from the illustrated embodiment and may extend for a relatively long length as compared to traditional implantable medical devices. The antenna 72 may be used for communication and/or as an RF collector to receive power to recharge the power source 20. Furthermore, while one antenna structure 72 is illustrated, multiple antennas may be provided to facilitate different types of communication; to have a -different antenna, for transmission versus reception; to provide a separate power collector, to provide low and high power communication formats, to provide redundancy or for any number of reasons. One or more antennas may also be included in the lead body 60. FIG. 3 illustrates an alternative embodiment, wherein a distal portion 80 of the tether 70 functions as a lead having an electrode 82 for sensing or stimulation. That is, the electrode 82 is electrically coupled to the housing 12 via iha distal portion 80 of the tether 70. This electrical coupling may be completely internal to and distinct from the tether 70 so that the mechanical properties of the tether 70 may be relied upon without adding stress or strain to what would be considered a lead body. Hie electrodes 62 and 82 may be positioned to facilitate defibrillation across the vector defined. In another embodiment, the electrode 82 acts as a pacing electrode. In yet another embodiment, element 82 is a sensor such as a pressure sensor. The antenna 72 of FIG- 2 is not illustrated, though such an antenna may also be provided when the tether 70 includes one or more electrodes and/or sensors. The structure of the tether 70 may vary over its length. The distal portion 80 is not intended to be severed. The proximal portion, in one embodiment, is intended to be severed; thus, a transition point 84 may be present. The tether 70 may have different materials and different construction from one portion to another or may have a unitary construction throughout

FΪG. 4 illustrates an embodiment having lead 60 and lead !00 extending from the distal header 15. The second lead 100 is illustrated as having a tined lip .110 for securemeni as well as a tip electrode 112 and ring electrode .114, FIG, 4 is meant to illustrate that multiple leads may depend from the distal header 16 and a variety of electrode and attachment (e.g., tines, helical tip) configurations may be employed. The use of two such ieads is not meant to be limiting and any number of additional leads may be provided. Though not illustrated, one or more additional electrodes may be present on tether 70, as illustrated in FlG, 3.

FΪG. 5 illustrates a sectional view of housing 12. In particular, multiple connection ports 150, 152,. .154 and 156 are illustrated in the proximal and distal .headers 14, .16. Port

150 includes a cavity 160 shaped to receive a male connecting pin from, e.g., a lead, A set screw .162 is positioned to advance into the cavity 160 and engage the connecting pin. thus securing the pin in place. Access to the set screw 162 is gained through a set screw opening 165 that may include a self sealing material- such as silicone to reduce fluid entry into the set screw opening after implantation. The configuration of port 150 is repeated in each of the illustrated ports 152. 154 and 156. More or fewer ports raay be provided as necessary and alternative configurations may be employed. When used to received and -insecure a lead 60, the lead pi.n will make contact with one or more electrical connectors disposed within cavity M(I The tether 70 may also include a connector pin thus allowing for connection to toe housing .12 in. the same manner as a lead. Of course, if the tether 70 includes electrode(s), antennas or other components appropriate electrical contact is made via the pin and cavity, ϊn the absence of such components, the tether is simply mechanically secured within the port 154, 156. As indicated, the tether 70 may be integrally formed with, the proximal header 14. thus appropriate access to ports 154, 156 (if provided) is facilitated by the configuration of the tether 70 or by providing access through a portion of the tether 70. FCCIS. 6A and 6B illustrate an alternative multiple lead configuration. In this embodiment, lead 60 is coupled with the distal header '16. A second lead U)O* is coupled with the proximal header 14 as is the tether 70. ϊn some applications, it may he desirable to have the second lead JOO* extend in the same direction, as the tether 70, and as such, connection to the proximal header 14 is straight forward. Alternatively, and as illustrated, the lead 100* is extended in the same direction as the first lead 60 (i.e., distal to the housing 12). When coupled with the proximal header 14, the lead !00v is bent to achieve this configuration. While this is non-problematic for the lead. .100*. movement of the housing 1.2 via the tether 70 (e.g., retracting the housing 12) may be more difficult. To permit and facilitate such movement, the lead 100* is bent to provide sufficient excess so that the housing 12 may move relative to the lsad 100" without affecting the tip placement

It should be appreciated the lead 60, extending from the distal header 16 also includes a certain amount of excess to address .normal movement of housing 12 caused by pulsitile blood flow as well as some movement caused by withdrawal or retraction of the tether 70. The curvature in the lead 100* may simply be imparted during implant, with the housing 1.2 remaining separate from the lead 100* other than at fee proximal header 14.

Alternatively, as illustrated in FiG. 6B, a guide member 180 may be provided on an outer portion of the housing 12. The lead 100' passes through the guide member .1 BO maintaining the lead 1.00* in close proximity to the housing despite the imparted curvature and any resulting bias. Jn addition, by appropriately sizing the guide member 180 and providing a material with a low coefficient of friction (e.g., paiylene, silicone) on the guide member 180 and/or the lead 100', the housing 12 may be slid relative to the lead 100'. For clarity, lead 60 is not shown in FlG. 6B, It should be appreciated that more than one bad may be coupled to the proximal header 14 in the manner illustrated. Furthermore, even if a single lead is employed, that lead may be coupled as illustrated by the lead 100' in FIGS. 6A and 68. This would allow all connections to be made at one end of the housing .12 while still permitting lead advancement in a direction opposite to that of the tether 70.

FlGS. 7 A and 7B illustrate a system including a device that will aid in positioning any of the illustrated leads as well as the housing 12. A steeraMe stylet (or catheter) 200 has a handle portion 202 at a proximal end that includes controls that cause the sty id to flex or bend to føciliiate intravascular navigation. A. releasable clamping member 210 is positioned at or near a distal end of the stylet 200. The clamping member is illustrated schematically in FlG. 7B as a sectional taken about the line A-A of FIG. 7A. Upon actuation of the handle portion 202. the clamping member 2K) opens and closes pivoting arms 212 so that lead 100* (or tether 7G) is gripped or released. In. this manner, the lead 100' is directed to a. target location, snά the clamping member 2iO is opened, releasing the lead 100*, ft should be appreciated that the stylet 200 could be navigated as an over the wire catheter,, thus following a previously positioned guklewire. The clamping of the lead 1.00* would remain the same; however, the stylet/catheter 200 would be guided by the guide wire as opposed to being navigated independently, As indicated, such a device may be used to position leads coupled with either the proximal head 14 or the distal header 16 and may be used to position the housing 12. To position the housing 12, the damping member may be secured to a portion of an attached lead or to the tether 70, Implantation in this manner will be facilitated if the clamping occurs relatively close to the housing 12, Alternatively, a lead extending from the distal header 16 may be gripped at any position distal to the housing 12, so that advancement of the lead with stylet 200 advances the housing 12 as well.

FIGS. SA - 8D illustrate another embodiment wherein a steerable stylet 250 is used to position the housing 1.2. FlG. SC is a sectional view taken about the line A-A in FlG. 8A and FlO. SD is a sectional view token about the line B-B in FI.G. SA. In this embodiment;, the tether 70 has a lumen 254 sized to receive the stylet 250. While the T- anehor 76 is illustrated as being coupled with the tether 70, it should he appreciated that the T-snchor 76 may be attached afterwards and hence is not utilized with the stylet 250 or the T-anchor 76 includes a thronghbore that aligns with the lumen 254, thereby permitting passage of the stylet 250. In this embodiment* an abutment 252 is provided on an exterior of the housing 1.2, as part of proximate header .14. Thus, as the stylet 250 extends through the luroen 254, the tip of the stylet 250 will eventually reach and strike the abutment 252, 5 Continued advancement of the stylet 250 will cause advancement of the housing 12 within a vasculature pathway. If advanced too far, the tether 70 may be retracted,, thus retracting the housing 12. As such, the housing 12 may be implanted at a target location by using the stylet 250 for forward advancement of the housing 12 and the tether 70 for any necessary retraction. Leads (not shown in these figures) may he implanted with the stylet

K) 200 previously described or similar mechanisms, if utilized. F.tG> SC also illustrates how the antenna 72 (if included) is positioned outside of the path defined by turners 254, which is congruent with abutment 252.

FIGS. 9ASD are similar to FIGS. M-ZD. In this embodiment the lumen 254 extends through the housing 1.2 as well as the lead 60. Thus, the stylet 250 may be

15 advanced all the way through the tether 70, the housing 12 and the lead 60 until it. abuts an end of the lead 60. Thus, navigation of the stylet 250 will direct the distal end of e.g., lead 60 which pulls the housing 12, ultimately positioning thai component as well.

FlGS. 9E - 9H illustrate an embodiment having multiple lumens 254a, 254b through tether 70, housing 12 and lead(s) 60, with the second lead not illustrated. In tliϊs

20 manner the stylet 250 can be directed through a specific lumen 254a.254, to engage a particular lead separately from another lead. As should he apparent more than two lumens 254a.254b may be provided to permit more than two leads or other appendages to be directly manipulated by the stylet 250. Further, ih$ size, spacing and configuration of the lumens 254.may be varied, ϊn an alternative arrangement, more lumens are provided

.25 through the housing 12 and coupled with a corresponding lead than are provided through the tether 70. That is, the stylet 250 is directed through a lumen in the tether 70 and into a larger opening within the proximal header 14. The tip of the stylet 250 is then manipulated to manually select from a plurality of lumens each extending from this opening through the bousing 1.2 to a particular lead.

30 While direct manipulation of the stylet 250 to select a desired rumen within the housing 12 is one option, alternative arrangements are available. For example, the tip of the styiet 250 may be sized or shaped to specifically engage only one lumen through ibs opening in the proximal header 1.4. For each such lumen engaged, the tip may be exchanged or a different stylet 250 may be -utilized. As an example, the largest tip may be inserted through the common lumen in the tether 70 and will only access the largest sub- lurnen passing through the housing 12. While occluding this larger opening, the next smaller tip may be utilized, and again a specific sub-Iuraen provides the only passage.

As described;, the IVMD IO may include multiple leads with each of these leads attached or coupled with ihe housing 12. Due to the ske and implant location oflVMD 10, particular configuration of the housing 12 may make attachment of more than two leads cumbersome. In fact in embodiments, the use of more than one lead may be cumbersome, fn such a case, the present invention provides for the use of multiple

IVMDs 10. each having one or two leads. The separate IVMDs 10 are in wireless communication so that their activities are synchronized. For example, one JVMD may provide atrial pacing aid another may provide ventricular pacing. The multiple IVMDs 10 may he completely independent and simply communicate to one another to synchronize timing. Alternatively, one IVMD 10 may act to control the functions of one or more other

IVMDs. The multiple IVMDs IO may be implanted through the same entry point and reside in the same anatomical location or proximate one another (e.g., both within the superior vena, cava but offset from one another). Alternatively, the multiple IVMDs may be implanted from different locations and reside remotely from one another, while retaining wireless communication.

FIG. 10 illustrates an embodiment wherein housing 12 is separated into two components 12a, 1.2b. Hie housing components .12a. 12b are operative).)-1 coupled together with a flexible interconnect 300. which may include one or more wires, cables or fibers for electrical or data communication. Alternatively,, the .flexible interconnect 300.may be a solely a mechanical coupling with, each housing component J 2a, 12b operating independently. For example, each may have separate functions. Alternatively., the housing components 12a, 12b axe mechanically coupled aid communicate in a wireless medium such as RF. Due to their close proximity, they may also be inductively coupled both for data communication and power transmission functions. Thus, the flexible interconnect 300 will mechanically connect the separate housing components 12a, 12b and may provide electrical data and/or power couplings. As such, the flexible interconnect 300 will act Hke tether 70' as between housing component 12a and housing component 12b. That is, securing the proximal end of tether 70' will ultimately retrain housing component 12b through the flexible interconnect 300.

FIG. 10 also schematically illustrates a simplified tether 70* as compared to lhs tether 70 illustrated in previous embodiments. Simplified tether 70' is a generally linear, flexible member such as wire or cord and may be monofilament or multi-fiiar. The simplified tether 70' could be secured to an anchor member such as the T~anchor 74 which is then secured to tissue. Alternatively, the simplified tether 70' could be sutured directly to tissue.

FlGB. 1 IA and 11 B illustrate another embodiment including multiple housing components 12a and 12b. As shown, housing component 12a includes the lead 60 extending from a distal end 16. The tether 70 extends in an opposite direction from the proximal end 14. A threaded receptacle 310 is axially aligned with a lumen 254 (FIGS. 8- 9) through the tether 70. The second housing component 12b includes a through bore 320 sized to receive the tether 70. Thus, the housing component 12b may be added to or removed front the component J 2a subsequent to implantation of component 12a.

The housing component 12a includes one or more receiving channels 314a, 314b that receive corresponding connector pins.3.! 2a.312b. The engagement of connector pins 312 within channels 314 allows for a mechanical coupling as well as optionally providing for electrical connection through one or all of the connections. The connector pins 312 are provided with biased protrusions 316a, 316b received within detents 31 $a? 318b: thus, locking the connectors pins 312 into the channels 314 when full inserted. Initial insertion as well as subsequent release of the connector pins 312 may require retraction of the protrusions 3 iβ internally via a mechanism that is not illustrated; thus, providing a secure locking mechanism. Alternatively, the spring bias of the protrusions 316 may be overcome by applying sufficient force in an axial direction. Thus, a locking action is formed that will maintain the connection of the two housing components 12a and 12b while implanted, but does not require additional components for engagement and/or disengagement. It should he appreciated that the size, shape, location, and configuration of the pins 3.12 and channels 314 may be varied in numerous ways while remaining within the spirit and scope of the present invention.

In FlG. I IB, housing component 12a is coupled with housing component 12b. Also illustrated is a stylet.322 having a threaded, tapered tip 326. The stylet 326 is mserted through the lumen 254 with the tether 70. The stylet 326 is advanced until the tip 326 reaches the threaded receptacle 31.0. Rotation of the stylet 326 then, causes the threaded tip 326 to engage the receptacle 3.10. Once so engaged, liner movement of the stylet 322 will correspondingly move the housing component 12a. (and 12b if coupled as illustrated). Furthermore, once fully engaged, rotation of lite stylet in a clockwise (with standard threading) direction will rotate the housing component ,i 2a. Use of the stylet 322 in this manner allows for greater positional control of the housing 1.2a. within the vasculature. While retraction of the tether 70 allows for gross movements, the engaged stylet 322 permits more precise .movement which facilitates the attachment or detachment of housing component 1.2b, among other things.

In one embodiment the stylet 322 Is advanced through the tether 70 and threaded into the receptacle 310, The housing receptacle 12b is then advanced over the tether 70 using another stylet (see e.g., FIG. !3B) to push the housing 12k When the housing components 12a, 12b are proximate one another, stylet 322 is used (alone or in combination wi ώ tether 70) to hold housing component 12a in place and rotate housing component 12a to align with housing component 12b. When so aligned, ths housing components 12a, 12b are joined. It should be appreciated that engagement mechanisms may be provided between housing member 12a. 1.2b that do not require specific alignment. That is, a retaining clip, channel or other member may extend ahoitt the circumference of the header of one housing component and a corresponding component may extend circumfereMially (folly or partially) about the corresponding header of the other housing component; thus, relative rotational positioning between the two housing components is irrelevant to engagement so long as general axial alignment is provided. For example, rather than having channel 314 discretely received a single pin 312? the channel 314 may extend circumferentiaUy around the proximal planar face of the housing component 12a.

Thus, the pin(s) 312 may be received anywhere along this channel 314. Relative rotation is permitted even when protrusions 316 and detent 318 (which may also be circumferential) are utilized. Alternatively, the detent(s) 31.8 may remain discrete and rotation of the housing components 12a, 12b will cause engagement. FIOS. 12A - 12 D illustrate another embodiment of stylet 322. FiGS. 12A - 12C are side sectional views of a tip portion of the stylet 322. Initial engagement of the threaded tip 326 may he made more difficult since th& housing component 12a h relatively free to rotate when implanted. The stylet 322 m the present embodiment includes an outer sheath 350 and an inner rod member 352. The threaded tapered tip 324 retracts and extends from the outer sheath 350.

One or more pins 340 extend from fee outer sheath 350, with two such pins 340a.

5 340b illustrated. The pins 340 are sixed to easily engage openings 342 (with 342a and

342h illustrated), ft should be appreciated that more openings 342 may be provided than pins 340 to again ease initial engagement. As illustrated, in FIGS. 12A imά 1.20, the tip 326 is initially retracted within the sheath 350 and fee stylet 322 is spaced from housing 1.2. The stylet 322 is advanced until the pins 340 engage the openings 342. as shown in

K) FTG. I2.& Rotation of the stylet 322 may be necessary to achieve this engagement

Again, the fit of the pin 340 to the opening 342 nesd not be particularly tight Subsequent rotation of the $tylet 322 will cause the pins 340 to abut & surface of the openings 342. Subsequently, the rod 352 may be advanced via control at a handle 360 and rotated so that tip 326 is threaded into the receptacle 310, thus achieving a secure engagement so that

15 subsequent manipulation of the styϊεt 322 will directly control the housing 12.

FIOS. 13A and 13B illustrate another embodiment utilizing multiple housing components 32a, 12b. In this embodiment the tether 70 is coupled with housing- component .12a and housing component 1.2b is slid, over the tether 70. A stylet/catheter 400 is provided that includes a lumen 410 sized to receive the tether 70. Thus, the stylet

20 400 is also slid over tether 70 and is used to push housing component 12b into engagement with .housing component 12a. Though, not separately shown* .it should be appreciated that the stylet 400 may be releasably secured to housing component 12b so that advancement retraction and rotation of the housing component 12b is facilitated, The manner in which stylet 400 is releasably secured to housing component 12b may vary and may include

25 without limitation any of the coupling arrangements discussed, herein.

FiG. 14 illustrates an embodiment of a multi component housing 12, wherein the distal housing component 12b includes a supplemental tether 450, Hie supplemental tether 450 may be permanent or temporary. In either case, the tether 450 may be used to retract housing component .12b while a device such as stylet 400 is used to advance the

30 housing component 12b, When, permanent, the supplemental tether 450 may be separately sutured at a distal end for secnrement or may simply be ailxed to the tether 70. FIG, 15 is an embodiment similar to that of FlG. 14. ϊn this embodiment the stylet 400 includes an outwardly extending tab 460. As the sly lei 400 is rotated (in either direction), the tab 460 will engage the secondary tether 450, causing the housing component 12b, to rotate wife the stylet 400. Thus, the stylet 400 is used to advance and rotate the housing component 12b, without any other coupling required and the secondary tether 450 is used to retract the housing component 12b.

More than two housing components may be coupled together to form or modify the IVMD 10. As previously indicated, different parts of the same device may be separated between housing components. Alternatively or In addition, subsequent housing components may be added, to provide additional therapies, diagnostics, capabilities or power. For example, an JVMD J 0 may be implanted with a single use (i.e., non~ rechargeable) battery, At a later point, another housing component may be added that includes a power supply to replace the depleted or soon to be depleted single use battery. Thus, the useful lifetime of a given device may be extended with a relatively minor procedure. An IVMD U) may initially be implanted having pacing functions and a later module may be added that provides defibrillation therapies. FlG. 16 illustrates one embodiment ofIVMD 10 having .(bur joined housing components 12a, 12b, 12c and 12d. Ii should be appreciated that any number may be joined using any combination of the embodiments discussed herein. It should further be appreciated that each such component need not have the same sisεe and shape. This will depend upon the components included i» any given section of housing 12 and may take advantage of variations in the vasculature anatomy.

The IVMD K) may also be accessed post implant to add components (as discussed above) or to exchange components. That is, rather than simply adding a housing component .12 having an additional battery 20, a housing portion 12 having the battery 20 is first removed over the tether 70 and a new housing portion 12 is added. In this manner, the Iead(s) 60 may remain in place, while other portions of the device are removed, replaced or otherwise manipulated To that end., it should be appreciated that the distal header .16 may take the form of a full or partial housing component 12 that remains in place and is tethered to allow other housing components to be manipulated. Alternatively, the tether 70 may be coupled with a distal portion of the Iead(s) or lead connector. Thus, the entire housing 12 may be added/removed while ihe 5ead(s) remains implanted and tethered Finally, it should be appreciated that the IVMD may provide a variety of functions including sensing, diagnostics and/or therapy. Thus, accessing the .1VMD IC) via the tether 70 allows for other components to be exchanged without removing the entirety of the device. For example, chemical sensors may become depleted of a source material or catalyst and replaced in this manner. Similarly, longer term drug elating member or drug reservoirs may be replaced. Such reservoirs may contain traditional pharmaceuticals and/or genetic materials or biologies. The JMVD K) may be used to deliver such agents (e.g., gene therapy) to a target tissue location. When necessary* the ΪVMD 10 is re- supplied without -requiring complete extraction or the implantation of another device. FIC-. 17 illustrates an. IVMD 10 implanted within the subclavian vein 504 and. extending into tlie superior vena cava 506 of a heart 500. The lead 60 is illustrated as being an atrial pacing lead and a distal tip 64 is affeed within the right atrium 502. Multiple additional leads may be included. The tether 70 extends from the proximal header 14 of the housing 1.2 through the subclavian vein 504. The proximal end 74 of έhe tether 70 exits the subclavian vein 504 at mx initial entry point 600. The proximal end 74 is secured to tissue surrounding the initial entry point 600, by e.g., the T-shaped anchor 76 which is sutured to the tissue. As pukitile blood, flow, directed towards the heart 500, and patient movement will cause movement of the bowsing 12, a sufficient amount of slack material is provided along the length of the tether 70. The position of housing 12 illustrated in FlG. 17 is noR-Hmiting. If desired, the housing 12 may be positioned closer to the initial, entry point (K)O5 thereby increasing the length of the lead 60. Conversely, the housing 12 may be positioned closer to or even within the heart 500, increasing the length of the tether 70 and decreasing the necessary length of the lead 60. FIG- 18 illustrates the position of the heart 500 relative to the subclavian vein 504 as well as the clavicle 620. M some embodiments, it may be desirable to position the housing 12 within the superior vena cava 506 below (towards the heart 500) the clavicle 620. This avoids any potential for "subclavian crush" wherein leads or components within the vasculature are compressed between the clavicle and the fust rib (not illustrated). The size and nature of a given IVMD .10 will determine whether this is or is not a concern. Due to its size, shape nnύ material properties, this will generally not affect the tether 70, Furthermore, implantation via the subclavian vein 304 is only one entry site and others may be utilized. As illustrated in FIG. 17. the initial entry point 600 may be positioned Quite distant relative to the location of the housing 12. FlG. 19 illustrates the position of the cephalic vein 660 which flows into ike subclavian vein.504 and is accessible along the arm 665 of the patient. Thus, the initial entry point.600 m&v be made in the cephalic vein 660 with the tether 70 then anchored to tissue in the arm 665.

After implantation, it. may be necessary or desirable to access the IVMD 10. The proximal md 74 of the tether 70 is located and, e.g.. the subclavian x;ein 504 is accessed. The housing 12 may be moved or removed/explanted via the tether 70 and any associated leads 60 can likewise be moved, explained, tested or otherwise manipulated- Ln addition. components may be added or replaced, on housing 12 without requiring removal As identification of the proximal end 74 of the tether 70 facilitates such procedures, the proximal end 74 may include a radiopaque marker for identification with various imaging technologies, such as X-ray imaging or fluoroscopy. Of course, the entirety of the tether 70 may likewise be radiopaque. Alternatively, or in addition thereto, the proximal end 74 may bs felt by applying pressure in the area. The configuration and anchoring of the proximal end 74 will determine whether this is possible and a balance is selected between patient perception of the proximal end, and the ability to locate the tether 70 manually, and the ease or pressure required to locate έhe tether manually 70. As yet another alternative, the subclavian vein 504 (or any vem/arte∑y with a tether 70) is accessed via anew puncture distal to the projdraaJ. end 74. The tether 70 is then located mid manipulated.

This may involve severing the tether 70 and if appropriate, reattaching or re-anchoring the tether 70.

As illustrated in FIG. 17, the IVMD 10 is secured at two locations; the first being where the proximal end 74 of the tether 70 is sutured and the second where the lead 60 is affixed to the atrial wall. In some embodiments, the nature of the lead 60 (or the absence thereof) may permit the distal end of that lead 60 or the housing 12 to move freely and remain unsecured. For example, lead 60 may include a pressure sensor or temperature sensor. While such sensors may still include an attachment mechanism, ii is possible to permit them to remain unattached. In addition to having the tether 70 anchored and having one or more leads 60 anchored, έhe flow of blood is directed towards έhε heart; which generally assists with maintaining the position of housing 12 as this ilow generates force against the anchored portion of the tether 70. This represents a relatively simple implantation procedure in that additional relent) on mechanisms are not required.

As indicated, the subclavian VQΪΏ.504 and superior vena cava 506 are not the only potential implant locations. A variety of other locations will be able to utilise blood flow a«d gravity in combination with the tether 70 to secure IVMD U). Of course, IVMD 10 may be implanted in other locations wherein this effect is not available or sufficient in addition, there may be other reasons to further secure various portions of IVMD 10. Jn one embodiment, retractable members are provided that expand against, a vessel wall to secure the IVMD 10. The retractable members are collapsed for subsequent movement or explantaiiøn. Sucb structures are illustrated in published PCT application WO

2004/110263 which is herein incorporated by reference.

FIG. 20 illustrates an IVMD 10 implanted in substantially the same position as illustrated in FIG. 17. In this embodiment, an expansion member 700 is expanded within the superior vena cava 506. Expansion member 700 presses the lead 60 against an interior wall of the vessel, further securing the lead 60 in place. Expansion member 700 may be a self expanding member made from shape-memory material or from material having a spring .force thai is restrained by e.g., a catheter until deployed. Alternatively, expansion member 700 is mechanically expanded by a balloon catheter or similar deployment mechanism. The iise of such a member is generally not required when both ends of the IYMD are secured and blood Sow is not pulling against an implanted lead. Such an expansion member may be useful when the lead 60 is otherwise unsecured or !VMB 10 is positioned in a location where blood flow or other forces might negatively affect the implant. It should be appreciated that the expansion member 700 may be used for one or more leads, the housing 12. the tether 70 or any combination thereof. FIGS. 21 A- 21 J schematically illustrate .implantation of the IVMD 10. In FIG.

2IA- a needle 810 is used to percutaneous!)' pierce and enter a vessel 802, such as for example the subclavian vein or cephalic vein. The needle 810 passes through the skin 800; in some cases access to the vein 802 may require piercing muscle or other tissue. Care is taken with the percutøneousiy puncture so that the needle does not pass entirely through the vessel 802 and into the underlying tissue 804.

With the needle 810 positioned within the vessel 802. a giudewire 815 is passed through the needle 810 and into the vessel as shown in FlG. 21 B. WMe retaining the guidewire 815 in place,, the needle 810 is withdrawn as illustrated in FIG. 21C. A deployment catheter 820 is inserted (FICJ-. 21D) into the vessel 802 over the guidewire 81.5. A dilation catheter may be used to expand, the original puncture or the {issue may be cut if the opening is insufficient. Depending upon the configuration of the ΪVMD i ϋ, the guidewire 815 and/or the deployment catheter 820 may be directed to the final implant location for a lead and/or for the housing of the ΪVMD 10. Alternatively,, il' a stylet or other externa! mechanism is utilized, the deployment catheter 820 need only provide access to the vessel 802 and the length of penetration is selected as desired.

The IVMD IO passes through the catheter 820 and enters the vessel 802. Again, multiple embodiments have been presented and the order of entry of certain components will vary accordingly. In this example, the lead 60 is directed first towards the implant site by e,g.5 a stylet directed through the lead or a stylet gripping an external portion of the lead; neither of which are illustrated in this figure. Trailing the lead 60 is the housing 12 followed by the tether 70. When the housing 1.2 and lead 60 are positioned, the tether 70 will include an. excess amount exiting the incision site as illustrated in FIG. 21F. If additional intravascular securement mechanisms are utilised, they are deployed and configured. The tether 70 is cut (FiG. 21G) at sever point 830 with a sufficient amount of excess provided so that upon anchoring, enough slack remains to allow expected movement of the IVlVlD 10 within the vasculature. The cut tether now has a new proximal end U(I

The new proximal end 840 is secured. As discussed, there are multiple methods to attach the tether 70. As illustrated, the T-anchor 76 is mechanically attached to the new proximal mά 840 (FlG. 21H). The T-anchor 76 is then secured with sutures 850 to tissue proximate the incision site (FIG. 211). The puncture or incision through the vessel 802 will heal around, the tether 70 and if necessary, this process may be aided by additional suturing or other techniques. The T-anchor 76 will remain below the surface 860 of the skin 800, with the actual depth/distance from the surface 860 determined by the medical practitioner, the depth of the incision,, and the site of implant. It should be appreciated that the anchor 76 may be affixed, to skin tissue, muscle or even the vasculature wall The .final position of the anchor 76 may therefore be subcutaneous or snbmuscuiar. As illustrated in

FIG. 211, the anchor 76 may be secured some distance from the vessel 802. This may require m additional minor incision, but allows the anchor point to be selected disparate from the puncture through the vessel 802.

FIGS, 22A and 22B are side elevaliorml sectional views that illustrate an. external vasculature anchor 900 (EV anchor). As previously discussed, the T-anchor 76 is sutured or otherwise attached to tissue external to the vessel 802. The EV anchor 900 is configured for direct attachment Io an external wall of the vessel 802. Hie EV anchor 900 has an. arcuate attachment pad 902 with a tether connection rod 904 depending therefrom. A tether attachment opening 906 is provided at a distal end of the rod 904 so that the tether 70 is coupleable to the rod 904. The rod 90 penetrates the vessel 802 (though the drawings are not meant to be to scale) and serves as the anchor .for the tether 70. The arcnate attachment pad 902 is large m comparison to the rod 904 so that the force generated against the ve$sel 802 is dispersed over a larger surface area.

The EV anchor 9(K) includes an interior concave surface 9.10 that is placed in contact with, the vessel wall. This surface 910 is subdivided into a first region 915 proximate the rod and the remainder of the surface 920. Various drug eluting or traditional coatings may be applied to the interior surface 910. For example, in the first region 915, where the rod 904 enters the vessel 802, adhesives.. steroids, coagulants or other materials are provided to facilitate the closure and. healing of the puncture. The second region 920 may be utilised for mors adhesion orsinipiy mechanical support. The attachment pad 902 is meant to generally conform to the shape of the exterior wall of the vessel 802. To that end, the pad 902 may be flexible or malleable. Furthermore, while illustrated as extending about less the half the- circumference of the vessels 802, it should be appreciated that fee pad 902 may extend about a greater portion of the vessel 802 and may completely surround the vessel 802, FJG. 23 is a flowchart with an overview of the steps for implanting the IVMD 10 consistent with the teachings of the present invention and as described in greater detail above. The appropriate point of entry (e.g., subclavian vein) is identiiled and a percutaneous puncture is made (KKK)). If, necessary, this opening is enlarged and any necessary catheter, gυidewire or siyiet is utilized to insert, deliver and attach the housing, leads and any other intravascular components of the IVMD 10 (1Oi 0). The tether 70 extends from the now delivered housing 12 to the entry site and excess tether is cut and discarded (1020). Finally, the tether is secure external to the vessel so as to anchor the IVMD 10 (1030).

While various embodiments have been shown and described, the present invention is not meant to be limited by these embodiments. .Furthermore, the embodiments may be combined in numerous ways without departing from the teachings of the present, invention, &vm when not specifically illustrated. Variations and modifications may be made without departing from the spirit and scope of the present invention.

Claims

We Claim:
1. An intravascular medical device (tVMD) comprising: an intravascular housing having a proximal end and a distal end; a circuit configured to operate the IVMD contained within the housing; a- .first lead coupled with the distal end and having a. fixation member at a distal end of the lead; and an elongated iether coupled with the proximal end of the housing.
2. The IVMO of d aim i fudher comprising: an electrode disposed along the tether and electrically coupled to the housing through the tether.
3. Hie IV MD of cl aim J , further comprising: sji antenna coupled to the circuit through the proximal end of the housing mid attached to the tether.
4. The IVMD of claim 3, wherein the antenna is disposed within the tether.
5. Hie IVMD of claim 1 , wherein the telher further comprises a tether lumen extending through an entirety of the tether.
6. The .IVMD of claim 5. wherein the housing further comprises a housing lumen extending through the housing wherein the housing ϊumert is coaxially aligned with the tether I umert.
7. The IVMD of claim <5, wherein the iead further comprises a lead lumen extending through at least a portion of {he first lead and the lead lumen is coaxially aligned with the housing lumen.
8. The IVMD of claim I, further comprising a second lead coupled with the distal end of the housing.
9 The IVMD of claim $L further comprising; a .first tether lumen extending through the tether; a .first housing lumen extending through the housing; a first lead lumen extending through the first lead; and a second lead lumen extending through the second lead.
1.0. The- IVMD of claim I, further comprising a tether anchor coupkable with a proximal end of the tether.
11. The IVMD of claim i O5, wherein the tether anchor is a T-shaped member including at least απe suturing location.
12. The IVMD of claim 10, wherein the tether anchor is a malleable, arcuate member having a rod depending from a concave surface, wherein the proximal mά of the tether is coupleable to the rod.
13. The ΪVMB of claim 1, wherein the IVMD is a pacemaker.
14. The IVMD of claim 3 , wherein the IVMD is a defibrillator.
15. The JVMD of claim L wherein the IVMD is a pacemaker and a defibrillator.
16. The IVMD of claim 1. wherein the housing has a diameter of approximately 6-7 French.
17. An intravascular medical device, comprising: a housing deployable within a vascular structure; means for delivering a therapy; means for securing the housing within the vasculature to a site exterior to the vasculature.
1 B. An intravascular medical device (IVMD) system comprising: a housing deployable within a vasculature structure; means for delivering therapy: means for securing the housing within the vasculature to a site exterior to the vasculature; and means for delivering the housing to an implant location within the vascular structure.
19. The ΪVMD system of claim .18> wherein the means for securing include a tether having a lumen and the means for delivering include a stylet configured for insertion through the lumen to direct movement of the housing.
20. The WMD of claim 18, wherein the means for delivering include a stylet having means for engaging an exterior of a lead coupled with t«e housing.
PCT/US2006/060556 2005-11-10 2006-11-02 Intravascular medical device WO2007059386A2 (en)

Priority Applications (3)

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EP2398556A2 (en) * 2009-02-20 2011-12-28 Endurance Rhythm, Inc. Implantable micro-generator devices with optimized configuration, methods of use, systems and kits therefor
EP2514481A1 (en) * 2009-12-14 2012-10-24 Terumo Kabushiki Kaisha Electric stimulation device
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US8543205B2 (en) 2010-10-12 2013-09-24 Nanostim, Inc. Temperature sensor for a leadless cardiac pacemaker
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CN103492022A (en) * 2011-04-04 2014-01-01 斯蒂维科技公司 Implantable lead
WO2014089299A3 (en) * 2012-12-05 2014-10-02 Perryman Laura Tyler Devices and methods for connecting implantable devices to wireless energy
CN104334231A (en) * 2012-05-08 2015-02-04 美敦力公司 Identifying lead insulation breaches and externalization of lead conductors
US9020611B2 (en) 2010-10-13 2015-04-28 Pacesetter, Inc. Leadless cardiac pacemaker with anti-unscrewing feature
US9060692B2 (en) 2010-10-12 2015-06-23 Pacesetter, Inc. Temperature sensor for a leadless cardiac pacemaker
US9126032B2 (en) 2010-12-13 2015-09-08 Pacesetter, Inc. Pacemaker retrieval systems and methods
US9168383B2 (en) 2005-10-14 2015-10-27 Pacesetter, Inc. Leadless cardiac pacemaker with conducted communication
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US9409029B2 (en) 2014-05-12 2016-08-09 Micron Devices Llc Remote RF power system with low profile transmitting antenna
US9409030B2 (en) 2011-01-28 2016-08-09 Micron Devices Llc Neural stimulator system
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US9623253B2 (en) 2012-07-17 2017-04-18 Micron Devices, LLC Devices and methods for treating urological disorders
US9802054B2 (en) 2012-08-01 2017-10-31 Pacesetter, Inc. Biostimulator circuit with flying cell
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US9072913B2 (en) 2005-10-14 2015-07-07 Pacesetter, Inc. Rate responsive leadless cardiac pacemaker
US10238883B2 (en) 2005-10-14 2019-03-26 Pacesetter Inc. Leadless cardiac pacemaker system for usage in combination with an implantable cardioverter-defibrillator
US7937148B2 (en) 2005-10-14 2011-05-03 Nanostim, Inc. Rate responsive leadless cardiac pacemaker
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US9872999B2 (en) 2005-10-14 2018-01-23 Pacesetter, Inc. Leadless cardiac pacemaker system for usage in combination with an implantable cardioverter-defibrillator
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US9687666B2 (en) 2005-10-14 2017-06-27 Pacesetter, Inc. Leadless cardiac pacemaker system for usage in combination with an implantable cardioverter-defibrillator
US8295939B2 (en) 2005-10-14 2012-10-23 Nanostim, Inc. Programmer for biostimulator system
US9216298B2 (en) 2005-10-14 2015-12-22 Pacesetter, Inc. Leadless cardiac pacemaker system with conductive communication
US8352025B2 (en) 2005-10-14 2013-01-08 Nanostim, Inc. Leadless cardiac pacemaker triggered by conductive communication
US9358400B2 (en) 2005-10-14 2016-06-07 Pacesetter, Inc. Leadless cardiac pacemaker
US8457742B2 (en) 2005-10-14 2013-06-04 Nanostim, Inc. Leadless cardiac pacemaker system for usage in combination with an implantable cardioverter-defibrillator
US9227077B2 (en) 2005-10-14 2016-01-05 Pacesetter, Inc. Leadless cardiac pacemaker triggered by conductive communication
US9409033B2 (en) 2005-10-14 2016-08-09 Pacesetter, Inc. Leadless cardiac pacemaker system for usage in combination with an implantable cardioverter-defibrillator
US9192774B2 (en) 2005-10-14 2015-11-24 Pacesetter, Inc. Cardiac pacemaker system for usage in combination with an implantable cardioverter-defibrillator
US8788035B2 (en) 2005-10-14 2014-07-22 Pacesetter, Inc. Leadless cardiac pacemaker triggered by conductive communication
US7627376B2 (en) 2006-01-30 2009-12-01 Medtronic, Inc. Intravascular medical device
US7616992B2 (en) 2006-01-30 2009-11-10 Medtronic, Inc. Intravascular medical device
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US9272155B2 (en) 2009-02-02 2016-03-01 Pacesetter, Inc. Leadless cardiac pacemaker with secondary fixation capability
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EP2398556B1 (en) * 2009-02-20 2016-08-24 Endurance Rhythm, Inc. Implantable micro-generator devices with optimized configuration
EP2398556A2 (en) * 2009-02-20 2011-12-28 Endurance Rhythm, Inc. Implantable micro-generator devices with optimized configuration, methods of use, systems and kits therefor
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WO2010138390A1 (en) * 2009-05-29 2010-12-02 Medtronic, Inc. Implantable medical device with exposed generator
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EP2514481A1 (en) * 2009-12-14 2012-10-24 Terumo Kabushiki Kaisha Electric stimulation device
EP2514481A4 (en) * 2009-12-14 2014-01-22 Terumo Corp Electric stimulation device
WO2011081699A1 (en) * 2009-12-30 2011-07-07 Cardiac Pacemakers, Inc. Tapered drug-eluting collar for a medical electrical lead
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US10188425B2 (en) 2010-12-13 2019-01-29 Pacesetter, Inc. Pacemaker retrieval systems and methods
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US10315039B2 (en) 2011-01-28 2019-06-11 Stimwave Technologies Incorporated Microwave field stimulator
US9199089B2 (en) 2011-01-28 2015-12-01 Micron Devices Llc Remote control of power or polarity selection for a neural stimulator
US10420947B2 (en) 2011-01-28 2019-09-24 Stimwave Technologies Incorporated Polarity reversing lead
US9409030B2 (en) 2011-01-28 2016-08-09 Micron Devices Llc Neural stimulator system
US9757571B2 (en) 2011-01-28 2017-09-12 Micron Devices Llc Remote control of power or polarity selection for a neural stimulator
CN103492022A (en) * 2011-04-04 2014-01-01 斯蒂维科技公司 Implantable lead
JP2014514069A (en) * 2011-04-04 2014-06-19 スティムウェイブ テクノロジーズ インコーポレイテッド Implantable lead
US10238874B2 (en) 2011-04-04 2019-03-26 Stimwave Technologies Incorporated Implantable lead
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US9242103B2 (en) 2011-09-15 2016-01-26 Micron Devices Llc Relay module for implant
US9974965B2 (en) 2011-09-15 2018-05-22 Micron Devices Llc Relay module for implant
US9511236B2 (en) 2011-11-04 2016-12-06 Pacesetter, Inc. Leadless cardiac pacemaker with integral battery and redundant welds
CN104334231A (en) * 2012-05-08 2015-02-04 美敦力公司 Identifying lead insulation breaches and externalization of lead conductors
US9839784B2 (en) 2012-05-08 2017-12-12 Medtronic, Inc. Identifying lead insulation breaches and externalization of lead conductors
US9956417B2 (en) 2012-05-08 2018-05-01 Medtronic, Inc. Identifying lead insulation breaches and externalization of lead conductors
US9623253B2 (en) 2012-07-17 2017-04-18 Micron Devices, LLC Devices and methods for treating urological disorders
US9802054B2 (en) 2012-08-01 2017-10-31 Pacesetter, Inc. Biostimulator circuit with flying cell
WO2014089299A3 (en) * 2012-12-05 2014-10-02 Perryman Laura Tyler Devices and methods for connecting implantable devices to wireless energy
US10369369B2 (en) 2012-12-05 2019-08-06 Stimwave Technologies Incorporated Devices and methods for connecting implantable devices to wireless energy
JP2016506255A (en) * 2012-12-05 2016-03-03 マイクロン デバイシーズ エルエルシー Apparatus and method for connecting an implantable device to wireless energy
US9409029B2 (en) 2014-05-12 2016-08-09 Micron Devices Llc Remote RF power system with low profile transmitting antenna
US10258800B2 (en) 2014-05-12 2019-04-16 Stimwave Technologies Incorporated Remote RF power system with low profile transmitting antenna

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