WO2003063955A1 - Electromagnetic trap for a lead - Google Patents

Electromagnetic trap for a lead Download PDF

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Publication number
WO2003063955A1
WO2003063955A1 PCT/US2003/002436 US0302436W WO03063955A1 WO 2003063955 A1 WO2003063955 A1 WO 2003063955A1 US 0302436 W US0302436 W US 0302436W WO 03063955 A1 WO03063955 A1 WO 03063955A1
Authority
WO
WIPO (PCT)
Prior art keywords
coil
electrical lead
medical electrical
signal
impedance
Prior art date
Application number
PCT/US2003/002436
Other languages
French (fr)
Inventor
Eduardo H. Villaseca
Garry L. Dublin
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
Application filed by Medtronic, Inc. filed Critical Medtronic, Inc.
Publication of WO2003063955A1 publication Critical patent/WO2003063955A1/en

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Classifications

    • 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
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00Electrotherapy; Circuits therefor
    • A61N1/02Details
    • A61N1/08Arrangements or circuits for monitoring, protecting, controlling or indicating
    • A61N1/086Magnetic resonance imaging [MRI] compatible leads
    • 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
    • A61N1/362Heart stimulators
    • A61N1/37Monitoring; Protecting
    • A61N1/3718Monitoring of or protection against external electromagnetic fields or currents
    • YGENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10TECHNICAL SUBJECTS COVERED BY FORMER USPC
    • Y10STECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
    • Y10S128/00Surgery
    • Y10S128/901Suppression of noise in electric signal

Definitions

  • This invention relates generally to implantable medical devices, and, more particularly, to a method and apparatus for trapping electromagnetic phenomenon resulting from electromagnetic fields experienced by a medical device lead.
  • implantable medical devices The technology explosion in the implantable medical devices industry has resulted in many new and innovative devices and methods for analyzing and improving the health of a patient.
  • the class of implantable medical devices now includes pacemakers, cardioverters, defibrillators, neural stimulators, and drug administering devices, among others.
  • Today's state-of-the-art implantable medical devices are vastly more sophisticated and complex than early ones, capable of performing significantly more complex tasks. The therapeutic benefits of such devices have been well proven.
  • implantable medical devices that provide data acquisition of important physiological data from a human body.
  • Many implantable medical devices are used for cardiac monitoring and therapy. Often these devices comprise sensors that are placed in blood vessels and/or chambers of the heart. Often these devices are operatively coupled with implantable monitors and therapy delivery devices.
  • implantable heart monitors and therapy delivery devices such as pace makers, cardioverter, defibrillators, heart pumps, cardiomyostimulators, ischemia treatment devices, drug delivery devices, and other heart therapy devices.
  • Most of these cardiac systems include electrodes for sensing and gain amplifiers for recording and/or driving sense event signals from the inter-cardiac or remote electrogram (EGM).
  • ECM inter-cardiac or remote electrogram
  • a number of physiological data such as ventricular pressure, oxygen supply in the patient's blood, EGM data, a patient's breathing patterns, and the like, are collected and stored by data acquisition devices implanted into a human body.
  • the data can then be used to analyze the condition of a patient's physical state.
  • information gathered by the implantable medical device may provide indications of certain conditions in a patient's body. Such conditions may affect the manner in which medical therapy (e.g., cardiac therapy) is delivered by the implantable medical device. If a particular condition is not detected properly, or a condition is misdiagnosed, incorrect reactions by the implantable medical device may occur. Incorrect reactions by the implantable medical device may cause harm to a patient.
  • medical therapy e.g., cardiac therapy
  • physiological data may be collected by a lead that delivers a signal relating to the physiological data to implantable medical device.
  • the signal on the lead may become corrupted, causing errors.
  • delivery of therapy may be performed in response to certain physiological data and/or data indicating other physical occurrences (e.g., unusual breathing patterns) detected in a patient.
  • certain activities performed by a patient may lead to increased physiological indications in the patient's body.
  • an implantable medical device may be programmed to detect such physiological changes and react to them accordingly.
  • an implantable medical device may deliver one or more cardiac therapy in response to a particular condition detected in the patient's body.
  • the implantable medical device may also modify the normal mode of therapy delivery in a patient's body in response to an unusual condition detected. Therefore, improved accuracy in the signal delivered by the lead is desirable for proper operation of the implantable medical device.
  • RF radio frequency
  • the length of the lead generally acts as an antenna during exposure to radio frequency signals, such as magnetic resonance imaging (MRI) processes. Due to the antenna-like behavior of the lead, the tip of the lead may behave as a source for the induced current flow created by the RF signal.
  • MRI magnetic resonance imaging
  • an appreciable amount of current may be generated in the lead such that the tip of the lead contains a sizable magnitude of current gradient. Due to the conservation of energy principles, much of the current is converted to heat due to the energy loss caused by the resistance of the lead tip. Therefore, a significant amount of heat may be generated at the tip of the lead, which may cause serious bodily injury to a patient. Burns to the tissue exposed to the tip of the lead may occur. Furthermore, a large amount of induced current in the lead may cause the implantable medical device to malfunction, thereby creating a risk of injury or death to the patient.
  • Changes to the signals traveling though the lead may cause the malfunctions in the operation of the implantable medical device.
  • erroneous delivery of therapy may occur which may lead to heart failure or other physiological damage to a patient.
  • the present invention is directed to overcoming, or at least reducing the effects of, one or more of the problems set forth above.
  • an apparatus for trapping an induced current resulting from an electromagnetic field in a medical electrical lead.
  • the medical electrical lead comprises an elongate body having a proximal and a distal end portion and a coil wound about the distal end, the coil to provide an electromagnetic trap for filtering radio frequency (RF) signal-induced currents.
  • RF radio frequency
  • a system for trapping an induced current resulting from an electromagnetic field in a medical electrical lead.
  • the system of the present invention comprises: an implantable medical device; and a medical electrical lead operatively coupled to the implantable medical device, the medical electrical lead having a proximal and a distal end portion and a coil wound about the distal end, the coil to provide an inductive impedance in parallel with a capacitive impedance for reducing induced currents resulting in the presence of an electromagnetic field.
  • a method for trapping an induced current resulting from an electromagnetic field in a medical electrical lead.
  • a wounded a coil is provided at a distal end of the medical electrical lead such that the coil provides an inductive impedance in parallel with a capacitive impedance to reduce the induced current.
  • Figure 1 is a simplified diagram of an implementation of an implantable medical device, in accordance with one illustrative embodiment of the present invention
  • Figure 2 illustrates a simplified block diagram representation of an implantable medical system in accordance with one illustrative embodiment of the present invention
  • Figure 3 illustrates a stylized depiction of a lead used in the implantable medical system, in accordance with one embodiment of the present invention
  • Figure 4 illustrates a stylized depiction of the distal end of the lead used in the implantable medical system, in accordance with one embodiment of the present invention
  • Figure 5 illustrates a stylized depiction of a coil implemented on the lead used in the implantable medical system, in accordance with one embodiment of the present invention
  • Figure 6 illustrates stylized depiction of a cross-sectional view of the coil implemented on the lead used in the implantable medical system, in accordance with one embodiment of the present invention.
  • Figures 7a, 7b, 7c, and 7d illustrate equivalent electrical circuit-diagram representations of the implementation of the coil placed on the lead used in the implantable medical system, in accordance with one embodiment of the present invention; While the invention is susceptible to various modifications and alternative forms, specific embodiments thereof have been shown by way of example in the drawings and are herein described in detail. It should be understood, however, that the description herein of specific embodiments is not intended to limit the invention to the particular forms disclosed, but on the contrary, the intention is to cover all modifications, equivalents, and alternatives falling within the spirit and scope of the invention as defined by the appended claims.
  • an implantable medical device includes collecting, storing, and analyzing physiological data relating to a patient, and/or delivering therapy (e.g., cardiac therapy) to a portion of a patient's body.
  • therapy e.g., cardiac therapy
  • these tasks are performed by an implantable medical system, which includes an implantable medical device.
  • one or more therapies may be delivered to a particular portion of a patient's body.
  • a therapy is a cardiac therapy, which is delivered to a patient's heart.
  • Embodiments of the present invention provide for reducing the induced current in a lead caused by RF signals present around the lead.
  • Embodiments of the present invention provide for inserting a coil proximate to the tip of the lead to reduce the length of the lead upon which an undesirable amount of current may be induced by RF signals.
  • Embodiments of the present invention provide for attaching a coil proximate to the tip of a lead, wherein an inductor in series with the resistivity of the lead is effectively created.
  • Embodiments of the present invention provide for a circuit whose effective resonance occurs at radio frequency signals such that an open circuit is created for radio frequency induced current signals present on the lead.
  • the coil provided by embodiments of the present invention provide an open circuit for high frequency signals, at the same time providing a normal signal path for low frequency signals such as pacing signals or data acquisition signals.
  • a sensor/therapy delivery device 210 placed upon the heart 116 of the human body 105 is used to acquire and process physiological data.
  • An implantable medical device 220 collects and processes a plurality of data acquired from the human body 105.
  • the implantable medical device 220 may be a pacemaker or a defibrillator.
  • the data acquired by the implantable medical device 220 can be monitored by an external system, such as the access device 240 comprising a programming head 122, which remotely communicates with the implantable medical device 220.
  • the programming head 122 is utilized in accordance with medical device programming systems known to those skilled in the art having the benefit of the present disclosure, for facilitating two-way communication between the pacemaker 220 and the access device 240.
  • a plurality of access devices 240 can be employed to collect a plurality of data processed by the implantable medical device 220 in accordance with embodiments of the present invention.
  • the pacemaker 220 is housed within a hermetically sealed, biologically inert outer canister or housing 113, which may itself be conductive so as to serve as an electrode in the pacemaker 220 pacing/sensing circuit.
  • One or more pacemaker sensors/leads are electrically coupled to the pacemaker 220 and extend into the patient's heart 116 via a vein 118.
  • the leads 114 Disposed generally near a distal end of the leads 114 are one or more exposed conductive electrodes (sensor/therapy delivery unit 210) for receiving electrical cardiac signals or delivering electrical pacing stimuli to the heart 116.
  • the leads 114 may be implanted with their distal end situated in either the atrium or ventricle of the heart 116.
  • the sensors 210, or the leads 114 associated with the sensors 210 may be situated in a blood vessel on the heart 116 via a vein 118.
  • the system 200 comprises a sensor/therapy delivery unit 210, an implantable medical device 220, and an access device 240.
  • Embodiments of the present invention provide a plurality of physiological data and non-physiological data from the sensor/therapy delivery unit 210 to the implantable medical device 220, which are then processed and stored in the implantable medical device 220.
  • the sensor/therapy delivery unit 210 may comprise a plurality of sensors that are capable of acquiring physiological and non-physiological data. Based upon data from the sensor(s) 210 and other factors, the implantable medical device 220 may deliver a therapy to a portion of the patient's body 105, via the sensor/therapy delivery unit 210.
  • the access device 240 which may communicate to the device 220 via an interface 230 (e.g., an interface internal to the device 220), can be used reprogram and/or make modifications to the operation of the implantable medical device 220.
  • a lead 114 (described below) coupled to the implantable medical device 220 is used to house the sensor(s) 210 and/or the therapy delivery electrodes.
  • a medical electrical lead 300 which may be coupled to the implantable medical device 220, is illustrated.
  • the lead 300 may be connected to an implantable medical device 220 at approximately the proximal end 320 of the lead 300.
  • the lead 300 also comprises a distal end 310 at the end of which is a tip 330.
  • radio frequency (RF) signal induced current present around the lead 300 may cause a current flow 340 in the lead 300.
  • RF radio frequency
  • the large amount of current 340 may be present at the tip 330, which causes an energy transfer due to the resistivity of the lead 300.
  • the energy transfer due to the resistivity of the lead 300 is transferred in the form of heat. This causes the tip 330 of the lead 300 to become heated. The heat from the tip 330 of the lead 300 may then be transferred to the tissues surrounding the tip 330, causing harm to the patient's body.
  • the induced current 340 generally occurs at the high RF frequencies, such as the MRI frequency of 64 MHz and/or 128 MHz. If the induced currents 340 were effectively blocked, the heat generated at the tip 330 would be substantially reduced.
  • a coil 410 is attached to the lead 300 near the tip 330 of the lead 300. Placing the coil 410 at the distal end 310 of the lead 300 may prevent appreciable amounts of high frequency induced current 340 from traveling on the length of the lead 300. Effectively, the coil 410 acts as an electromagnetic trap, which is capable of trapping/filtering RF signal-induced currents 340, such as currents induced by the presence of an MRI signal. Inductive and capacitive effects due to the implementation of the coil 410 (described in greater detail below) reduce the flow of high-frequency currents 340 through the tip 330 of the lead 300. Therefore, heat generated due to the high- frequency current's 340 interaction with the resistivity of the lead 300 is reduced as a result of the implementation of the coil 410.
  • the coil 410 is wrapped around the lead 300 near the tip 330.
  • the coil 410 provides the function of an inductor, whose inductive properties occur at higher signal frequencies, such as 64 and/or 128 MHz.
  • the outer diameter of the spool of the coil 410 may be approximately 50 to 60 thousandths of an inch.
  • the length of the coil 410 may be approximately one tenth of an inch. It should be appreciated that other measurements may be implemented to achieve the results taught by embodiments of the present invention.
  • the amount of windings of the coil 410 can be varied to affect the capacitive and inductive effects created by the coil 410. Therefore, the windings of the coil 410 can be adjusted to provide capacitive and inductive properties for a variety of frequencies of currents resulting from electromagnetic fields.
  • the coil 410 is made up of a wire that is insulated.
  • the wire within the coil 410 comprises conductive materials such as copper. It should be appreciated that a variety of conductive materials 610 may be used in accordance with embodiments of the present invention.
  • an insulated coating may be used in accordance with embodiments of the present invention.
  • the conductive material 610 of the coil 410 provides for electrical characteristics within the electrical path of the lead 300. In other words, the conductive material 610 of the coil 410 adds capacitive and or inductive characteristics to the electrical path of the lead 300 in a series fashion.
  • the coil 410 provides an equivalent inductance in series with the electrical flow path of the lead 300, as illustrated in Figure 7 A.
  • the insulative layer 620 of the coil 410 prevents the coil 410 from providing parallel electrical properties to the lead 300.
  • the coil 410 provides an inductor L 720 in series with an equivalent resistance R 710 in the electrical path of the lead 300, which terminates at the ring tip 330.
  • the inductor L 710 effectively becomes effective during the presence of an RF signal, such as an MRI signal of 64 MHz and/or 128 MHz. It should be appreciated the frequency at which the inductor L 710 becomes effective may be modified by changing the winding of the coil 410 and remain within the spirit of embodiments of the present invention. At low frequencies, such as a signal delivering a pacing signal to the tip 330 of the lead 300, the inductance L 710 is an equivalent electrical-short within the lead 300. As RF signal frequency signals surround the lead 300, the inductor L 710 provides an inductance of various measurements, depending on the windings and/or the size of the conductive material 610 of the wire associated with the coil 410.
  • an RF signal such as an MRI signal of 64 MHz and/or 128 MHz.
  • the inductor L 710 is a 4.7 micro Henry inductor, which is effectively created during the presence of an MRI signal field. This electrical effect is also present during pulse with radio frequency signals.
  • the 4.7 micro Henry inductor may reduce the instantaneous build-up of high- frequency currents induced by significant electromagnetic fields, such as fields caused by an MRI process.
  • the coil 410 is wound and designed such that the inductor L 710 created by the coil 410 is at a resonance frequency with radio frequency signals such as 64 MHz and 128 MHz signals. Therefore, at RF signal frequencies a large amount of impedance is present in the lead 300, thereby providing a large obstacle for RF induced currents in the lead 300. Effectively, an open circuit is created at the location of the inductor L 710 (for high-frequency currents) during the presence of high frequency signal.
  • the high impedance near the tip 330 of the lead 300 provided by the coil 410 at high frequencies causes most of the length of the lead 300 to be ineffective for inducement of signals caused by RF signals.
  • the coil 410 allows the passage of low frequency signals utilized by the implantable medical device 220.
  • the inductive reactance provided by the inductor L 710 significantly attenuates high frequency (radio frequency) induced signals in the lead 300.
  • FIG 7B an alternative embodiment of the equivalent circuit provided by the coil 410 at the tip 330 of the lead 300 is illustrated.
  • the coil 410 may be wound in such a manner around the lead 300 that a capacitance C 730 is also created.
  • the capacitance C 730 exists in parallel across the inductor L 710.
  • the capacitance C 730 and the inductor L 710 are in series with equivalent resistance R 720 of the lead 300.
  • the capacitance C 730 is generally due to the parasitic capacitance that is formed across each of the windings of the coil 410. Generally, the capacitance C 730 is effective during the presence of high-frequency signals at the tip 330 of the lead 300. The capacitance C 730 generally does not interfere with low-frequency signals on the lead 300, such as pacing signals sent by the implantable medical device 220 and/or physiological sensor signals traveling to the device 220.
  • the capacitance C 730 represents an equivalent capacitance of a combination of the plurality of parasitic capacitance across the windings of the coil 410.
  • the combination of the parallel configuration of the inductor L 710 and the capacitor C 730 provides a parallel circuit that is of a higher impedance than the inductor L 710 by itself. Therefore, the circuit provided by the coil 410 provides for a broader range of frequencies in which significant high impedance at high frequencies is created near the tip 330 of the lead 300.
  • the inductor L 710 and the capacitor C 730 provides a self- resonant circuitry that reacts to a range of RF signals, particularly to 64 MHz and/or to 128 MHz signals.
  • the resonance causes a high impedance reaction at the RF signal range such that currents induced by the RF signals are significantly attenuated.
  • the attenuation of the high frequency currents provides the benefit of preventing heating at the tip 330 of the lead 300.
  • the low-frequency current (Iiow req) 740 flows through the lead 300 through the resistor R 720, which is the equivalent resistance of the lead 300. Therefore, low-frequency signals, such as pacing signals and/or therapy delivery signals, can flow through the lead 300 and through the tip 330 to the tissue surrounding the tip 330. In other words, the coil 410 generally does not interfere with normal operation of therapy delivery and/or physiological data collection performed by the implantable medical device 220. However, at high frequencies, the inductor L 710 and/or the capacitance C 730 provide an open circuit (see Figures 7C and 7D).
  • the current induced by RF signals (Ihi g h_freq) is approximately zero due to the resonance nature of the impedance provided by the inductor L 710 and the capacitance C 730.
  • the equivalent circuitry provided by Figure 7 significantly reduces the high frequency currents in the leads 300 due to exposure to radio frequency signals, such as MRI signals, while allowing normal operation of the implantable medical device 220.

Abstract

A method and an apparatus for trapping induced current resulting from an electromagnetic field. Embodiments of the present invention provide for an elongate body having a proximal and a distal end portion and a coil wound about the distal end, the coil to provide an electromagnetic trap for filtering radio frequency (RF) signal-induced currents.

Description

ELECTROMAGNETIC TRAP FOR A LEAD
This invention relates generally to implantable medical devices, and, more particularly, to a method and apparatus for trapping electromagnetic phenomenon resulting from electromagnetic fields experienced by a medical device lead.
The technology explosion in the implantable medical devices industry has resulted in many new and innovative devices and methods for analyzing and improving the health of a patient. The class of implantable medical devices now includes pacemakers, cardioverters, defibrillators, neural stimulators, and drug administering devices, among others. Today's state-of-the-art implantable medical devices are vastly more sophisticated and complex than early ones, capable of performing significantly more complex tasks. The therapeutic benefits of such devices have been well proven.
There are many implementations of implantable medical devices that provide data acquisition of important physiological data from a human body. Many implantable medical devices are used for cardiac monitoring and therapy. Often these devices comprise sensors that are placed in blood vessels and/or chambers of the heart. Often these devices are operatively coupled with implantable monitors and therapy delivery devices. For example, such cardiac systems include implantable heart monitors and therapy delivery devices, such as pace makers, cardioverter, defibrillators, heart pumps, cardiomyostimulators, ischemia treatment devices, drug delivery devices, and other heart therapy devices. Most of these cardiac systems include electrodes for sensing and gain amplifiers for recording and/or driving sense event signals from the inter-cardiac or remote electrogram (EGM).
Generally, a number of physiological data such as ventricular pressure, oxygen supply in the patient's blood, EGM data, a patient's breathing patterns, and the like, are collected and stored by data acquisition devices implanted into a human body. The data can then be used to analyze the condition of a patient's physical state. Many times, information gathered by the implantable medical device may provide indications of certain conditions in a patient's body. Such conditions may affect the manner in which medical therapy (e.g., cardiac therapy) is delivered by the implantable medical device. If a particular condition is not detected properly, or a condition is misdiagnosed, incorrect reactions by the implantable medical device may occur. Incorrect reactions by the implantable medical device may cause harm to a patient. Generally, physiological data may be collected by a lead that delivers a signal relating to the physiological data to implantable medical device. In the presence of an electromagnetic field, the signal on the lead may become corrupted, causing errors. Many times, delivery of therapy may be performed in response to certain physiological data and/or data indicating other physical occurrences (e.g., unusual breathing patterns) detected in a patient. For example, certain activities performed by a patient may lead to increased physiological indications in the patient's body. Often, an implantable medical device may be programmed to detect such physiological changes and react to them accordingly. For example, an implantable medical device may deliver one or more cardiac therapy in response to a particular condition detected in the patient's body. The implantable medical device may also modify the normal mode of therapy delivery in a patient's body in response to an unusual condition detected. Therefore, improved accuracy in the signal delivered by the lead is desirable for proper operation of the implantable medical device.
When an implantable medical device has been inserted into a patient's body, it enters an area where the patient is exposed to a substantial amount of radio frequency (RF) signals. The length of the lead generally acts as an antenna during exposure to radio frequency signals, such as magnetic resonance imaging (MRI) processes. Due to the antenna-like behavior of the lead, the tip of the lead may behave as a source for the induced current flow created by the RF signal.
In the presence of MRI signals, (e.g., during MRI scanning processes), an appreciable amount of current may be generated in the lead such that the tip of the lead contains a sizable magnitude of current gradient. Due to the conservation of energy principles, much of the current is converted to heat due to the energy loss caused by the resistance of the lead tip. Therefore, a significant amount of heat may be generated at the tip of the lead, which may cause serious bodily injury to a patient. Burns to the tissue exposed to the tip of the lead may occur. Furthermore, a large amount of induced current in the lead may cause the implantable medical device to malfunction, thereby creating a risk of injury or death to the patient.
Changes to the signals traveling though the lead (e.g. , sensor signals from the lead to the implantable medical device and/or therapy signals sent by the device) may cause the malfunctions in the operation of the implantable medical device. In such an instance, erroneous delivery of therapy may occur which may lead to heart failure or other physiological damage to a patient.
The present invention is directed to overcoming, or at least reducing the effects of, one or more of the problems set forth above.
SUMMARY OF THE INVENTION In one aspect of the present invention, an apparatus is provided for trapping an induced current resulting from an electromagnetic field in a medical electrical lead. The medical electrical lead comprises an elongate body having a proximal and a distal end portion and a coil wound about the distal end, the coil to provide an electromagnetic trap for filtering radio frequency (RF) signal-induced currents.
In another aspect of the present invention, a system is provided for trapping an induced current resulting from an electromagnetic field in a medical electrical lead. The system of the present invention comprises: an implantable medical device; and a medical electrical lead operatively coupled to the implantable medical device, the medical electrical lead having a proximal and a distal end portion and a coil wound about the distal end, the coil to provide an inductive impedance in parallel with a capacitive impedance for reducing induced currents resulting in the presence of an electromagnetic field.
In yet another aspect of the present invention, a method is provided for trapping an induced current resulting from an electromagnetic field in a medical electrical lead. A wounded a coil is provided at a distal end of the medical electrical lead such that the coil provides an inductive impedance in parallel with a capacitive impedance to reduce the induced current.
BRIEF DESCRIPTION OF THE DRAWINGS The inventions may be understood by reference to the following description taken in conjunction with the accompanying drawings, in which like reference numerals identify like elements, and in which:
Figure 1 is a simplified diagram of an implementation of an implantable medical device, in accordance with one illustrative embodiment of the present invention; Figure 2 illustrates a simplified block diagram representation of an implantable medical system in accordance with one illustrative embodiment of the present invention; Figure 3 illustrates a stylized depiction of a lead used in the implantable medical system, in accordance with one embodiment of the present invention;
Figure 4 illustrates a stylized depiction of the distal end of the lead used in the implantable medical system, in accordance with one embodiment of the present invention; Figure 5 illustrates a stylized depiction of a coil implemented on the lead used in the implantable medical system, in accordance with one embodiment of the present invention;
Figure 6 illustrates stylized depiction of a cross-sectional view of the coil implemented on the lead used in the implantable medical system, in accordance with one embodiment of the present invention; and
Figures 7a, 7b, 7c, and 7d illustrate equivalent electrical circuit-diagram representations of the implementation of the coil placed on the lead used in the implantable medical system, in accordance with one embodiment of the present invention; While the invention is susceptible to various modifications and alternative forms, specific embodiments thereof have been shown by way of example in the drawings and are herein described in detail. It should be understood, however, that the description herein of specific embodiments is not intended to limit the invention to the particular forms disclosed, but on the contrary, the intention is to cover all modifications, equivalents, and alternatives falling within the spirit and scope of the invention as defined by the appended claims.
DETAILED DESCRIPTION OF SPECIFIC EMBODIMENTS Illustrative embodiments of the invention are described below. In the interest of clarity, not all features of an actual implementation are described in this specification. It will of course be appreciated that in the development of any such actual embodiment, numerous implementation-specific decisions must be made to achieve the developers' specific goals, such as compliance with system-related and business-related constraints, which will vary from one implementation to another. Moreover, it will be appreciated that such a development effort might be complex and time-consuming, but would nevertheless be a routine undertaking for those of ordinary skill in the art having the benefit of this disclosure.
There are many discrete processes involving the operation of implantable medical devices (e.g., pacemakers, cardio defibrillators, and the like). The operation of an implantable medical device includes collecting, storing, and analyzing physiological data relating to a patient, and/or delivering therapy (e.g., cardiac therapy) to a portion of a patient's body. Often, these tasks are performed by an implantable medical system, which includes an implantable medical device. Based upon the analysis performed by the implantable medical system, one or more therapies may be delivered to a particular portion of a patient's body. One example of such a therapy is a cardiac therapy, which is delivered to a patient's heart. Interpretation of the physiological data and/or data relating to unusual activities in the patient's body is important in determining the behavior (e.g., therapy deliver patterns, etc.) of the implantable medical device. Embodiments of the present invention provide for reducing the induced current in a lead caused by RF signals present around the lead. Embodiments of the present invention provide for inserting a coil proximate to the tip of the lead to reduce the length of the lead upon which an undesirable amount of current may be induced by RF signals. Embodiments of the present invention provide for attaching a coil proximate to the tip of a lead, wherein an inductor in series with the resistivity of the lead is effectively created.
Embodiments of the present invention provide for a circuit whose effective resonance occurs at radio frequency signals such that an open circuit is created for radio frequency induced current signals present on the lead. In other words, the coil provided by embodiments of the present invention provide an open circuit for high frequency signals, at the same time providing a normal signal path for low frequency signals such as pacing signals or data acquisition signals.
Turning now to Figure 1, one embodiment of implementing an implantable medical device into a human body is illustrated. A sensor/therapy delivery device 210 (e.g., devices attached to leads 114) placed upon the heart 116 of the human body 105 is used to acquire and process physiological data. An implantable medical device 220 collects and processes a plurality of data acquired from the human body 105. In one embodiment, the implantable medical device 220 may be a pacemaker or a defibrillator. The data acquired by the implantable medical device 220 can be monitored by an external system, such as the access device 240 comprising a programming head 122, which remotely communicates with the implantable medical device 220. The programming head 122 is utilized in accordance with medical device programming systems known to those skilled in the art having the benefit of the present disclosure, for facilitating two-way communication between the pacemaker 220 and the access device 240.
In one embodiment, a plurality of access devices 240 can be employed to collect a plurality of data processed by the implantable medical device 220 in accordance with embodiments of the present invention. The pacemaker 220 is housed within a hermetically sealed, biologically inert outer canister or housing 113, which may itself be conductive so as to serve as an electrode in the pacemaker 220 pacing/sensing circuit. One or more pacemaker sensors/leads, collectively identified with reference numeral 114 in Figure 1, are electrically coupled to the pacemaker 220 and extend into the patient's heart 116 via a vein 118. Disposed generally near a distal end of the leads 114 are one or more exposed conductive electrodes (sensor/therapy delivery unit 210) for receiving electrical cardiac signals or delivering electrical pacing stimuli to the heart 116. The leads 114 may be implanted with their distal end situated in either the atrium or ventricle of the heart 116. In an alternative embodiment, the sensors 210, or the leads 114 associated with the sensors 210, may be situated in a blood vessel on the heart 116 via a vein 118.
Turning now to Figure 2, a system 200, in accordance with one embodiment of the present invention, is illustrated. The system 200 comprises a sensor/therapy delivery unit 210, an implantable medical device 220, and an access device 240. Embodiments of the present invention provide a plurality of physiological data and non-physiological data from the sensor/therapy delivery unit 210 to the implantable medical device 220, which are then processed and stored in the implantable medical device 220. The sensor/therapy delivery unit 210 may comprise a plurality of sensors that are capable of acquiring physiological and non-physiological data. Based upon data from the sensor(s) 210 and other factors, the implantable medical device 220 may deliver a therapy to a portion of the patient's body 105, via the sensor/therapy delivery unit 210. The access device 240, which may communicate to the device 220 via an interface 230 (e.g., an interface internal to the device 220), can be used reprogram and/or make modifications to the operation of the implantable medical device 220. In one embodiment, a lead 114 (described below) coupled to the implantable medical device 220 is used to house the sensor(s) 210 and/or the therapy delivery electrodes.
Turning now to Figure 3, a medical electrical lead 300, which may be coupled to the implantable medical device 220, is illustrated. The lead 300 may be connected to an implantable medical device 220 at approximately the proximal end 320 of the lead 300. The lead 300 also comprises a distal end 310 at the end of which is a tip 330. As illustrated in Figure 3, radio frequency (RF) signal induced current present around the lead 300 may cause a current flow 340 in the lead 300. At the tip 330, a current source is effectively created due to the RF signals present around the lead 300.
In the presence of significant electro-magnetic fields, such as fields present during an MRI processes, a substantial amount of RF signal-induced current may be present around the tip 330 of the lead 300. Therefore, the large amount of current 340 may be present at the tip 330, which causes an energy transfer due to the resistivity of the lead 300. Generally, the energy transfer due to the resistivity of the lead 300 is transferred in the form of heat. This causes the tip 330 of the lead 300 to become heated. The heat from the tip 330 of the lead 300 may then be transferred to the tissues surrounding the tip 330, causing harm to the patient's body. The induced current 340 generally occurs at the high RF frequencies, such as the MRI frequency of 64 MHz and/or 128 MHz. If the induced currents 340 were effectively blocked, the heat generated at the tip 330 would be substantially reduced.
Turning now to Figure 4, a coil 410 is attached to the lead 300 near the tip 330 of the lead 300. Placing the coil 410 at the distal end 310 of the lead 300 may prevent appreciable amounts of high frequency induced current 340 from traveling on the length of the lead 300. Effectively, the coil 410 acts as an electromagnetic trap, which is capable of trapping/filtering RF signal-induced currents 340, such as currents induced by the presence of an MRI signal. Inductive and capacitive effects due to the implementation of the coil 410 (described in greater detail below) reduce the flow of high-frequency currents 340 through the tip 330 of the lead 300. Therefore, heat generated due to the high- frequency current's 340 interaction with the resistivity of the lead 300 is reduced as a result of the implementation of the coil 410.
Turning now to Figure 5, an enlarged view of the distal end 310 of the lead 300 and the coil 410, is illustrated. The coil 410 is wrapped around the lead 300 near the tip 330. The coil 410 provides the function of an inductor, whose inductive properties occur at higher signal frequencies, such as 64 and/or 128 MHz. As an example, the outer diameter of the spool of the coil 410 may be approximately 50 to 60 thousandths of an inch. The length of the coil 410 may be approximately one tenth of an inch. It should be appreciated that other measurements may be implemented to achieve the results taught by embodiments of the present invention. The amount of windings of the coil 410 can be varied to affect the capacitive and inductive effects created by the coil 410. Therefore, the windings of the coil 410 can be adjusted to provide capacitive and inductive properties for a variety of frequencies of currents resulting from electromagnetic fields.
In one embodiment, the coil 410 is made up of a wire that is insulated. Turning now to Figure 6, a cross sectional view of a portion of the coil 410 is illustrated. In one embodiment, the wire within the coil 410 comprises conductive materials such as copper. It should be appreciated that a variety of conductive materials 610 may be used in accordance with embodiments of the present invention. Furthermore, an insulated coating
620 that insulates the wire 610 is a dielectric material, such as an enamel coating. Due to the insulation of the coil 410, the portion of the lead 300 covered by the coil 410 is not electrically conducted to its surrounding, therefore, it does not function as an anode or an electrical return path of current into the body of the patient. However, the conductive material 610 of the coil 410 provides for electrical characteristics within the electrical path of the lead 300. In other words, the conductive material 610 of the coil 410 adds capacitive and or inductive characteristics to the electrical path of the lead 300 in a series fashion.
Turning now to Figures 7A - 7D, equivalent electrical circuitry that result from the implementation of the coil 410 onto the lead 300, are illustrated. In one embodiment, the coil 410 provides an equivalent inductance in series with the electrical flow path of the lead 300, as illustrated in Figure 7 A. As mentioned above, the insulative layer 620 of the coil 410 prevents the coil 410 from providing parallel electrical properties to the lead 300. The coil 410 provides an inductor L 720 in series with an equivalent resistance R 710 in the electrical path of the lead 300, which terminates at the ring tip 330. The inductor L
710 effectively becomes effective during the presence of an RF signal, such as an MRI signal of 64 MHz and/or 128 MHz. It should be appreciated the frequency at which the inductor L 710 becomes effective may be modified by changing the winding of the coil 410 and remain within the spirit of embodiments of the present invention. At low frequencies, such as a signal delivering a pacing signal to the tip 330 of the lead 300, the inductance L 710 is an equivalent electrical-short within the lead 300. As RF signal frequency signals surround the lead 300, the inductor L 710 provides an inductance of various measurements, depending on the windings and/or the size of the conductive material 610 of the wire associated with the coil 410. In one embodiment, the inductor L 710 is a 4.7 micro Henry inductor, which is effectively created during the presence of an MRI signal field. This electrical effect is also present during pulse with radio frequency signals. The 4.7 micro Henry inductor may reduce the instantaneous build-up of high- frequency currents induced by significant electromagnetic fields, such as fields caused by an MRI process.
Generally, the coil 410 is wound and designed such that the inductor L 710 created by the coil 410 is at a resonance frequency with radio frequency signals such as 64 MHz and 128 MHz signals. Therefore, at RF signal frequencies a large amount of impedance is present in the lead 300, thereby providing a large obstacle for RF induced currents in the lead 300. Effectively, an open circuit is created at the location of the inductor L 710 (for high-frequency currents) during the presence of high frequency signal. The high impedance near the tip 330 of the lead 300 provided by the coil 410 at high frequencies, causes most of the length of the lead 300 to be ineffective for inducement of signals caused by RF signals. At the same time, the coil 410 allows the passage of low frequency signals utilized by the implantable medical device 220. The inductive reactance provided by the inductor L 710 significantly attenuates high frequency (radio frequency) induced signals in the lead 300. Turning now to Figure 7B, an alternative embodiment of the equivalent circuit provided by the coil 410 at the tip 330 of the lead 300 is illustrated. The coil 410 may be wound in such a manner around the lead 300 that a capacitance C 730 is also created. The capacitance C 730 exists in parallel across the inductor L 710. The capacitance C 730 and the inductor L 710 are in series with equivalent resistance R 720 of the lead 300. The capacitance C 730 is generally due to the parasitic capacitance that is formed across each of the windings of the coil 410. Generally, the capacitance C 730 is effective during the presence of high-frequency signals at the tip 330 of the lead 300. The capacitance C 730 generally does not interfere with low-frequency signals on the lead 300, such as pacing signals sent by the implantable medical device 220 and/or physiological sensor signals traveling to the device 220.
The capacitance C 730 represents an equivalent capacitance of a combination of the plurality of parasitic capacitance across the windings of the coil 410. The combination of the parallel configuration of the inductor L 710 and the capacitor C 730 provides a parallel circuit that is of a higher impedance than the inductor L 710 by itself. Therefore, the circuit provided by the coil 410 provides for a broader range of frequencies in which significant high impedance at high frequencies is created near the tip 330 of the lead 300. In one embodiment, the inductor L 710 and the capacitor C 730 provides a self- resonant circuitry that reacts to a range of RF signals, particularly to 64 MHz and/or to 128 MHz signals. The resonance causes a high impedance reaction at the RF signal range such that currents induced by the RF signals are significantly attenuated. The attenuation of the high frequency currents provides the benefit of preventing heating at the tip 330 of the lead 300. By changing the thickness of the conductive material 610 in the coil 410 and/or changing the number of windings of the coil 410, the self-resonant circuitry can be designed to react, at a variety of predetermined range of high frequency signals. This principle can be used to adapt embodiments of the present invention to respond to changing frequency implementation of MRI processes. As shown in Figure 7C, at low frequencies, the low-frequency current (Iiow req) 740 flows through the lead 300 through the resistor R 720, which is the equivalent resistance of the lead 300. Therefore, low-frequency signals, such as pacing signals and/or therapy delivery signals, can flow through the lead 300 and through the tip 330 to the tissue surrounding the tip 330. In other words, the coil 410 generally does not interfere with normal operation of therapy delivery and/or physiological data collection performed by the implantable medical device 220. However, at high frequencies, the inductor L 710 and/or the capacitance C 730 provide an open circuit (see Figures 7C and 7D).
At high frequencies, the current induced by RF signals (Ihigh_freq) is approximately zero due to the resonance nature of the impedance provided by the inductor L 710 and the capacitance C 730. The equivalent circuitry provided by Figure 7 significantly reduces the high frequency currents in the leads 300 due to exposure to radio frequency signals, such as MRI signals, while allowing normal operation of the implantable medical device 220.
The above detailed description is an illustrative example of an embodiment in accordance with the present invention, of the implementation of the implantable medical device 220 described above. It should be appreciated that other implementations and/or embodiments can be employed within the spirit of the present invention. The teachings of the present invention can be utilized for a variety of systems relating to electrical circuitry, including circuitry that utilize stored charge.
The particular embodiments disclosed above are illustrative only, as the invention may be modified and practiced in different but equivalent manners apparent to those skilled in the art having the benefit of the teachings herein. Furthermore, no limitations are intended to the details of construction or design herein shown, other than as described in the claims below. It is therefore evident that the particular embodiments disclosed above may be altered or modified and all such variations are considered within the scope and spirit of the invention. Accordingly, the protection sought herein is set forth in the claims below.

Claims

WHAT IS CLAIMED:
1. A medical electrical lead, comprising: an elongate body having a proximal and a distal end portion and a coil wound about said distal end, said coil to provide an electromagnetic trap for filtering radio frequency (RF) signal-induced currents.
2. The medical electrical lead of claim 1 , wherein said coil to provide an electromagnetic trap for filtering RF signal-induced currents resulting from the presence of a magnetic resonance imaging (MRI) signal.
3. The medical electrical lead of claim 1 , wherein said coil comprises: a conductive wire; and an electrically insulative layer surrounding said conductive wire.
4. The medical electrical lead of claim 3, wherein said medical electrical lead comprising an equivalent resistance.
5. The medical electrical lead of claim 4, wherein said coil to provide an inductive impedance in series with said equivalent resistance.
6. The medical electrical lead of claim 5, wherein said inductive impedance is active during the presence of a radio frequency signal.
7. The medical electrical lead of claim 6, wherein said inductive impedance is active during the presence of a electromagnetic field resulting from at least one of a 64 MHz and a 128 MHz signal.
8. The medical electrical lead of claim 5, wherein said coil to provide a capacitive impedance in parallel with said inductive impedance, wherein said inductive impedance and said capacitive impedance from a parallel circuit in series with said equivalent resistance.
9. The medical electrical lead of claim 8, wherein said capacitive impedance is active during the presence of a radio frequency signal.
10. The medical electrical lead of claim 9, wherein said capacitive impedance is active during the presence of a electromagnetic field resulting from at least one of a 64
MHz and a 128 MHz signal.
11. The medical electrical lead of claim 8, wherein said inductive and capacitive impedance to provide a self-resonant circuitry during the presence of an RF signal.
12. A medical electrical lead, comprising: an elongate body having a proximal and a distal end portion and a coil wound about said distal end, said coil to provide an inductive impedance in parallel with a capacitive impedance for reducing induced currents resulting in the presence of an electromagnetic field .
13. The medical electrical lead of claim 12, wherein said inductive and said capacitive impedance are active during the presence of a electromagnetic field resulting from at least one of a 64 MHz and a 128 MHz signal.
14. The medical electrical lead of claim 12, wherein said coil comprises: a conductive wire; and an electrically insulative layer surrounding said conductive wire.
15. The medical electrical lead of claim 12, wherein said inductive and capacitive impedances to provide a self-resonant circuitry during the presence of an RF signal.
16. A implantable medical device system, comprising: an implantable medical device; and a medical electrical lead operatively coupled to said implantable medical device, said medical electrical lead having a proximal and a distal end portion and a coil wound about said distal end, said coil to provide an inductive impedance in parallel with a capacitive impedance for reducing induced currents resulting in the presence of an electromagnetic field.
17. The implantable medical device system of claim 17, wherein said inductive impedance and said capacitive impedance to form a filter to pass a sensor signal and to block said induced current.
18. The implantable medical device system of claim 17, wherein said inductive impedance and said capacitive impedance to form a filter to pass a pacing signal and to block said induced current.
19. The implantable medical device system of claim 17, wherein said inductive and capacitive impedance to provide a self-resonant circuitry during the presence of an said electromagnetic, said self-resonant circuitry to block an induced current resulting from an RF signal within a pre-determined range of frequency.
20. A method for trapping an radio frequency (RF) signal induced current on a medical electrical lead, comprising: providing a wound coil at a distal end of said medical electrical lead such that said coil provides an inductive impedance in parallel with a capacitive impedance to reduce said induced current.
21. The method of claim 20, wherein winding said coil at said distal end of said medical electrical lead further comprises winding said coil such that a self resonating circuit comprising an inductive impedance and a capacitive impedance is active in the presence of said RF signal.
22. The method of claim 21 , wherein winding said coil at said distal end of said medical electrical lead further comprises winding said coil such that said self resonating circuit is active in the presence of at least one of a 64 MHz and a 128 MHz signal.
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Cited By (39)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7844344B2 (en) 2004-03-30 2010-11-30 Medtronic, Inc. MRI-safe implantable lead
US7844343B2 (en) 2004-03-30 2010-11-30 Medtronic, Inc. MRI-safe implantable medical device
US7853332B2 (en) 2005-04-29 2010-12-14 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US7877150B2 (en) 2004-03-30 2011-01-25 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US8027736B2 (en) 2005-04-29 2011-09-27 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US8244375B2 (en) 2008-08-25 2012-08-14 Pacesetter, Inc. MRI compatible lead
US8280526B2 (en) 2005-02-01 2012-10-02 Medtronic, Inc. Extensible implantable medical lead
US8483842B2 (en) 2007-04-25 2013-07-09 Medtronic, Inc. Lead or lead extension having a conductive body and conductive body contact
US8543207B2 (en) 2004-12-17 2013-09-24 Cardiac Pacemakers, Inc. MRI operation modes for implantable medical devices
US8554335B2 (en) 2007-12-06 2013-10-08 Cardiac Pacemakers, Inc. Method and apparatus for disconnecting the tip electrode during MRI
US8565874B2 (en) 2009-12-08 2013-10-22 Cardiac Pacemakers, Inc. Implantable medical device with automatic tachycardia detection and control in MRI environments
US8897875B2 (en) 2007-12-06 2014-11-25 Cardiac Pacemakers, Inc. Selectively connecting the tip electrode during therapy for MRI shielding
US8897887B2 (en) 2006-06-08 2014-11-25 Greatbatch Ltd. Band stop filter employing a capacitor and an inductor tank circuit to enhance MRI compatibility of active medical devices
US8977356B2 (en) 2009-02-19 2015-03-10 Cardiac Pacemakers, Inc. Systems and methods for providing arrhythmia therapy in MRI environments
US8989840B2 (en) 2004-03-30 2015-03-24 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US9044593B2 (en) 2007-02-14 2015-06-02 Medtronic, Inc. Discontinuous conductive filler polymer-matrix composites for electromagnetic shielding
US9108066B2 (en) 2008-03-20 2015-08-18 Greatbatch Ltd. Low impedance oxide resistant grounded capacitor for an AIMD
US9155877B2 (en) 2004-03-30 2015-10-13 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US9186499B2 (en) 2009-04-30 2015-11-17 Medtronic, Inc. Grounding of a shield within an implantable medical lead
US9248283B2 (en) 2001-04-13 2016-02-02 Greatbatch Ltd. Band stop filter comprising an inductive component disposed in a lead wire in series with an electrode
US9295828B2 (en) 2001-04-13 2016-03-29 Greatbatch Ltd. Self-resonant inductor wound portion of an implantable lead for enhanced MRI compatibility of active implantable medical devices
US9427596B2 (en) 2013-01-16 2016-08-30 Greatbatch Ltd. Low impedance oxide resistant grounded capacitor for an AIMD
US9463317B2 (en) 2012-04-19 2016-10-11 Medtronic, Inc. Paired medical lead bodies with braided conductive shields having different physical parameter values
US9561378B2 (en) 2008-10-02 2017-02-07 Cardiac Pacemakers, Inc. Implantable medical device responsive to MRI induced capture threshold changes
US9731119B2 (en) 2008-03-12 2017-08-15 Medtronic, Inc. System and method for implantable medical device lead shielding
USRE46699E1 (en) 2013-01-16 2018-02-06 Greatbatch Ltd. Low impedance oxide resistant grounded capacitor for an AIMD
US9931514B2 (en) 2013-06-30 2018-04-03 Greatbatch Ltd. Low impedance oxide resistant grounded capacitor for an AIMD
US9993638B2 (en) 2013-12-14 2018-06-12 Medtronic, Inc. Devices, systems and methods to reduce coupling of a shield and a conductor within an implantable medical lead
US10080889B2 (en) 2009-03-19 2018-09-25 Greatbatch Ltd. Low inductance and low resistance hermetically sealed filtered feedthrough for an AIMD
US10155111B2 (en) 2014-07-24 2018-12-18 Medtronic, Inc. Methods of shielding implantable medical leads and implantable medical lead extensions
US10279171B2 (en) 2014-07-23 2019-05-07 Medtronic, Inc. Methods of shielding implantable medical leads and implantable medical lead extensions
US10350421B2 (en) 2013-06-30 2019-07-16 Greatbatch Ltd. Metallurgically bonded gold pocket pad for grounding an EMI filter to a hermetic terminal for an active implantable medical device
US10537730B2 (en) 2007-02-14 2020-01-21 Medtronic, Inc. Continuous conductive materials for electromagnetic shielding
US10559409B2 (en) 2017-01-06 2020-02-11 Greatbatch Ltd. Process for manufacturing a leadless feedthrough for an active implantable medical device
US10561837B2 (en) 2011-03-01 2020-02-18 Greatbatch Ltd. Low equivalent series resistance RF filter for an active implantable medical device utilizing a ceramic reinforced metal composite filled via
US10589107B2 (en) 2016-11-08 2020-03-17 Greatbatch Ltd. Circuit board mounted filtered feedthrough assembly having a composite conductive lead for an AIMD
US10905888B2 (en) 2018-03-22 2021-02-02 Greatbatch Ltd. Electrical connection for an AIMD EMI filter utilizing an anisotropic conductive layer
US10912945B2 (en) 2018-03-22 2021-02-09 Greatbatch Ltd. Hermetic terminal for an active implantable medical device having a feedthrough capacitor partially overhanging a ferrule for high effective capacitance area
US11198014B2 (en) 2011-03-01 2021-12-14 Greatbatch Ltd. Hermetically sealed filtered feedthrough assembly having a capacitor with an oxide resistant electrical connection to an active implantable medical device housing

Families Citing this family (117)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9061139B2 (en) * 1998-11-04 2015-06-23 Greatbatch Ltd. Implantable lead with a band stop filter having a capacitor in parallel with an inductor embedded in a dielectric body
US6701176B1 (en) 1998-11-04 2004-03-02 Johns Hopkins University School Of Medicine Magnetic-resonance-guided imaging, electrophysiology, and ablation
US8527046B2 (en) 2000-04-20 2013-09-03 Medtronic, Inc. MRI-compatible implantable device
US8509913B2 (en) 2001-04-13 2013-08-13 Greatbatch Ltd. Switched diverter circuits for minimizing heating of an implanted lead and/or providing EMI protection in a high power electromagnetic field environment
US7853325B2 (en) * 2001-04-13 2010-12-14 Greatbatch Ltd. Cylindrical bandstop filters for medical lead systems
US8989870B2 (en) 2001-04-13 2015-03-24 Greatbatch Ltd. Tuned energy balanced system for minimizing heating and/or to provide EMI protection of implanted leads in a high power electromagnetic field environment
US7899551B2 (en) * 2001-04-13 2011-03-01 Greatbatch Ltd. Medical lead system utilizing electromagnetic bandstop filters
US7787958B2 (en) * 2001-04-13 2010-08-31 Greatbatch Ltd. RFID detection and identification system for implantable medical lead systems
US8712544B2 (en) 2001-04-13 2014-04-29 Greatbatch Ltd. Electromagnetic shield for a passive electronic component in an active medical device implantable lead
US8219208B2 (en) * 2001-04-13 2012-07-10 Greatbatch Ltd. Frequency selective passive component networks for active implantable medical devices utilizing an energy dissipating surface
US8977355B2 (en) * 2001-04-13 2015-03-10 Greatbatch Ltd. EMI filter employing a capacitor and an inductor tank circuit having optimum component values
US8457760B2 (en) 2001-04-13 2013-06-04 Greatbatch Ltd. Switched diverter circuits for minimizing heating of an implanted lead and/or providing EMI protection in a high power electromagnetic field environment
US20070088416A1 (en) 2001-04-13 2007-04-19 Surgi-Vision, Inc. Mri compatible medical leads
WO2003102614A1 (en) 2002-05-29 2003-12-11 Surgi-Vision, Inc. Magnetic resonance probes
US20050288752A1 (en) * 2003-08-25 2005-12-29 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US8868212B2 (en) * 2003-08-25 2014-10-21 Medtronic, Inc. Medical device with an electrically conductive anti-antenna member
US20050283213A1 (en) * 2003-08-25 2005-12-22 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US20050288751A1 (en) * 2003-08-25 2005-12-29 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
US20050070972A1 (en) * 2003-09-26 2005-03-31 Wahlstrand Carl D. Energy shunt for producing an MRI-safe implantable medical device
US8332011B2 (en) * 2003-09-29 2012-12-11 Medtronic, Inc. Controlling blanking during magnetic resonance imaging
US7174219B2 (en) * 2004-03-30 2007-02-06 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US7912552B2 (en) * 2004-07-12 2011-03-22 Medtronic, Inc. Medical electrical device including novel means for reducing high frequency electromagnetic field-induced tissue heating
WO2006023700A2 (en) * 2004-08-20 2006-03-02 Biophan Technologies, Inc. Magnetic resonance imaging interference immune device
US8825180B2 (en) * 2005-03-31 2014-09-02 Medtronic, Inc. Medical electrical lead with co-radial multi-conductor coil
US7561906B2 (en) * 2005-05-04 2009-07-14 Boston Scientific Neuromodulation Corporation Electrical lead for an electronic device such as an implantable device
WO2007008301A2 (en) * 2005-07-12 2007-01-18 Biophan Technologies, Inc. Medical device with an electrically conductive anti-antenna member
EP1933933B1 (en) 2005-10-21 2018-11-28 MRI Interventions, Inc. Mri-safe high impedance lead systems
US8255054B2 (en) * 2005-11-04 2012-08-28 Kenergy, Inc. MRI compatible implanted electronic medical device
US8233985B2 (en) * 2005-11-04 2012-07-31 Kenergy, Inc. MRI compatible implanted electronic medical device with power and data communication capability
US7917213B2 (en) * 2005-11-04 2011-03-29 Kenergy, Inc. MRI compatible implanted electronic medical lead
WO2007102893A2 (en) * 2005-11-11 2007-09-13 Greatbatch Ltd. Tank filters placed in series with the lead wires or circuits of active medical devices to enhance mri compatibility
US8224462B2 (en) 2005-11-11 2012-07-17 Greatbatch Ltd. Medical lead system utilizing electromagnetic bandstop filters
US7853324B2 (en) * 2005-11-11 2010-12-14 Greatbatch Ltd. Tank filters utilizing very low K materials, in series with lead wires or circuits of active medical devices to enhance MRI compatibility
US20070179582A1 (en) * 2006-01-31 2007-08-02 Marshall Mark T Polymer reinforced coil conductor for torque transmission
US9901731B2 (en) * 2006-01-31 2018-02-27 Medtronic, Inc. Medical electrical lead having improved inductance
US7693568B2 (en) 2006-03-30 2010-04-06 Medtronic, Inc. Medical device sensing and detection during MRI
US7933662B2 (en) * 2006-04-26 2011-04-26 Marshall Mark T Medical electrical lead including an inductance augmenter
US9042999B2 (en) * 2006-06-08 2015-05-26 Greatbatch Ltd. Low loss band pass filter for RF distance telemetry pin antennas of active implantable medical devices
US8903505B2 (en) 2006-06-08 2014-12-02 Greatbatch Ltd. Implantable lead bandstop filter employing an inductive coil with parasitic capacitance to enhance MRI compatibility of active medical devices
US8116862B2 (en) 2006-06-08 2012-02-14 Greatbatch Ltd. Tank filters placed in series with the lead wires or circuits of active medical devices to enhance MRI compatibility
US20070299490A1 (en) * 2006-06-23 2007-12-27 Zhongping Yang Radiofrequency (rf)-shunted sleeve head and use in electrical stimulation leads
US9020610B2 (en) * 2006-06-23 2015-04-28 Medtronic, Inc. Electrode system with shunt electrode
US7734354B1 (en) 2006-08-04 2010-06-08 Advanced Neuromodulation Systems, Inc. Stimulation lead, stimulation system, and method for limiting MRI induced current in a stimulation lead
US9468750B2 (en) 2006-11-09 2016-10-18 Greatbatch Ltd. Multilayer planar spiral inductor filter for medical therapeutic or diagnostic applications
US9031670B2 (en) * 2006-11-09 2015-05-12 Greatbatch Ltd. Electromagnetic shield for a passive electronic component in an active medical device implantable lead
US9827415B2 (en) 2006-11-09 2017-11-28 Greatbatch Ltd. Implantable lead having multi-planar spiral inductor filter
US8239041B2 (en) 2010-08-02 2012-08-07 Greatbatch Ltd. Multilayer helical wave filter for medical therapeutic or diagnostic applications
DE102007022333A1 (en) 2007-05-12 2008-11-13 Biotronik Crm Patent Ag Electrode e.g. nuero-stimulation electrode, for intervention purposes, has casing surrounding supply line, where materials of pole and casing are made such that materials contain conductive particles in concentration embedded in matrix
US8386057B2 (en) 2006-11-17 2013-02-26 Biotronik Crm Patent Ag Electrode catheter for interventional use
DE102007034990A1 (en) * 2006-11-17 2008-06-12 Biotronik Crm Patent Ag Electrode catheter for interventional purposes
US7610101B2 (en) * 2006-11-30 2009-10-27 Cardiac Pacemakers, Inc. RF rejecting lead
US7962224B1 (en) 2007-02-05 2011-06-14 Advanced Neuromodulation Systems, Inc. Stimulation lead, stimulation system, and method for limiting MRI-induced current in a stimulation lead
WO2008115383A2 (en) 2007-03-19 2008-09-25 Boston Scientific Neuromodulation Corporation Methods and apparatus for fabricating leads with conductors and related flexible lead configurations
ES2462741T3 (en) * 2007-03-19 2014-05-26 Boston Scientific Neuromodulation Corporation MRI and RF compatible cables and related cable operation and manufacturing methods
EP2131393A4 (en) * 2007-03-23 2011-08-31 Fujitsu Ltd Electronic device, electronic apparatus mounting electronic device, article mounting electronic device, and method for manufacturing electronic device
US8103347B2 (en) 2007-04-25 2012-01-24 Advanced Neuromodulation Systems, Inc. Implantable pulse generator comprising MRI current limiting windings in header structure
US8032230B1 (en) 2007-10-09 2011-10-04 Advanced Neuromodulation Systems, Inc. Stimulation lead, stimulation system, and method for limiting MRI induced current in a stimulation lead
US8275464B2 (en) 2007-12-06 2012-09-25 Cardiac Pacemakers, Inc. Leads with high surface resistance
WO2009076169A2 (en) * 2007-12-06 2009-06-18 Cardiac Pacemakers, Inc. Implantable lead with shielding
AU2008335462B2 (en) * 2007-12-06 2014-02-20 Cardiac Pacemakers, Inc. Implantable lead having a variable coil conductor pitch
US20090179716A1 (en) * 2008-01-09 2009-07-16 Anaren, Inc. RF Filter Device
JP5149399B2 (en) * 2008-02-06 2013-02-20 カーディアック ペースメイカーズ, インコーポレイテッド Lead with design features compatible with MRI
US8311637B2 (en) * 2008-02-11 2012-11-13 Cardiac Pacemakers, Inc. Magnetic core flux canceling of ferrites in MRI
US8255055B2 (en) * 2008-02-11 2012-08-28 Cardiac Pacemakers, Inc. MRI shielding in electrodes using AC pacing
US8160717B2 (en) 2008-02-19 2012-04-17 Cardiac Pacemakers, Inc. Model reference identification and cancellation of magnetically-induced voltages in a gradient magnetic field
US8483840B2 (en) * 2008-03-20 2013-07-09 Greatbatch Ltd. Dual function tuned L-C input trap passive EMI filter component network for an active implantable medical device
US8412351B2 (en) * 2008-03-21 2013-04-02 Medtronic, Inc. System and method for shunting induced currents in an electrical lead
US20090270956A1 (en) * 2008-04-25 2009-10-29 Pacesetter, Inc. Implantable medical lead configured for improved mri safety
US20090281592A1 (en) * 2008-05-08 2009-11-12 Pacesetter, Inc. Shaft-mounted rf filtering elements for implantable medical device lead to reduce lead heating during mri
US8103360B2 (en) 2008-05-09 2012-01-24 Foster Arthur J Medical lead coil conductor with spacer element
WO2009143444A1 (en) * 2008-05-22 2009-11-26 The Ohio State University Mobile mangnetic traps and platforms for micro/nano particle manipulation
JP2012506725A (en) * 2008-10-23 2012-03-22 カーディアック ペースメイカーズ, インコーポレイテッド System for detecting changes in implantable medical device configuration affecting MRI conditional safety and detection method thereof
WO2010051265A1 (en) * 2008-10-30 2010-05-06 Greatbatch Ltd. Capacitor and inductor elements physically disposed in series whose lumped parameters are electrically connected in parallel to form a bandstop filter
US20100114275A1 (en) * 2008-10-30 2010-05-06 Pacesetter, Inc. Implantable medical lead including winding for improved mri safety
US8447414B2 (en) 2008-12-17 2013-05-21 Greatbatch Ltd. Switched safety protection circuit for an AIMD system during exposure to high power electromagnetic fields
US8285396B2 (en) * 2009-01-05 2012-10-09 Kenergy, Inc. MRI compatible electrical lead for an implanted electronic medical device
CA2754045C (en) 2009-03-04 2021-04-06 Imricor Medical Systems, Inc. Mri compatible electrode circuit
US8855788B2 (en) 2009-03-04 2014-10-07 Imricor Medical Systems, Inc. MRI compatible electrode circuit
US8805540B2 (en) 2009-03-04 2014-08-12 Imricor Medical Systems, Inc. MRI compatible cable
US8843213B2 (en) 2009-03-04 2014-09-23 Imricor Medical Systems, Inc. MRI compatible co-radially wound lead assembly
US8831743B2 (en) 2009-03-04 2014-09-09 Imricor Medical Systems, Inc. MRI compatible electrode circuit
US8761899B2 (en) 2009-03-04 2014-06-24 Imricor Medical Systems, Inc. MRI compatible conductive wires
US9084883B2 (en) * 2009-03-12 2015-07-21 Cardiac Pacemakers, Inc. Thin profile conductor assembly for medical device leads
US8463407B2 (en) * 2009-03-26 2013-06-11 Kenergy, Inc. MRI compatible implanted lead-electrode interface
WO2012116265A2 (en) * 2011-02-24 2012-08-30 MRI Interventions, Inc. Mri-guided catheters
EP2445577B1 (en) 2009-06-26 2015-08-05 Cardiac Pacemakers, Inc. Medical device lead including a unifilar coil with improved torque transmission capacity and reduced mri heating
US8601672B2 (en) * 2009-07-31 2013-12-10 Advanced Neuromodulation Systems, Inc. Method for fabricating a stimulation lead to reduce MRI heating
US8335572B2 (en) * 2009-10-08 2012-12-18 Cardiac Pacemakers, Inc. Medical device lead including a flared conductive coil
WO2011043898A2 (en) * 2009-10-09 2011-04-14 Cardiac Pacemakers, Inc. Mri compatible medical device lead including transmission line notch filters
US9254380B2 (en) 2009-10-19 2016-02-09 Cardiac Pacemakers, Inc. MRI compatible tachycardia lead
US9750944B2 (en) * 2009-12-30 2017-09-05 Cardiac Pacemakers, Inc. MRI-conditionally safe medical device lead
JP2013516221A (en) * 2009-12-30 2013-05-13 カーディアック ペースメイカーズ, インコーポレイテッド Apparatus for selectively increasing the inductance of an inner conductor of a medical device lead
WO2011081701A1 (en) * 2009-12-30 2011-07-07 Cardiac Pacemakers, Inc. Implantable electrical lead including a cooling assembly to dissipate mri induced electrode heat
US8391994B2 (en) 2009-12-31 2013-03-05 Cardiac Pacemakers, Inc. MRI conditionally safe lead with low-profile multi-layer conductor for longitudinal expansion
EP2519305B1 (en) 2009-12-31 2017-07-05 Cardiac Pacemakers, Inc. Mri conditionally safe lead with multi-layer conductor
US8914096B2 (en) * 2010-02-11 2014-12-16 Biotronik Se & Co. Kg Adaptation probe for insertion into implanted electrode devices of active medical implants and set composed of an implantable electrode device and an adaptation probe
WO2011123005A1 (en) * 2010-03-31 2011-10-06 St. Jude Medical Ab Medical implantable lead
EP2380489A1 (en) 2010-04-26 2011-10-26 Biotronik CRM Patent AG Discharge device and MRI-safe catheter system
US8834657B2 (en) 2010-08-20 2014-09-16 Kenergy, Inc. Method of manufacturing an mri compatible conductive lead body
US8825181B2 (en) 2010-08-30 2014-09-02 Cardiac Pacemakers, Inc. Lead conductor with pitch and torque control for MRI conditionally safe use
US8644932B2 (en) 2010-10-29 2014-02-04 Medtronic, Inc. Assessing a lead based on high-frequency response
US8831740B2 (en) 2010-11-02 2014-09-09 Pacesetter, Inc. Implantable lead assembly having a plurality of inductors
WO2012067713A1 (en) 2010-11-18 2012-05-24 Cardiac Pacemakers, Inc. Insulative structure for mri compatible leads
US8509915B2 (en) * 2010-12-17 2013-08-13 Biotronik Se & Co. Kg Implantable electrode line device for reducing undesirable effects of electromagnetic fields
US8612021B2 (en) 2011-02-10 2013-12-17 Medtronic, Inc. Magnetic resonance imaging compatible medical electrical lead and method of making the same
WO2012163414A1 (en) 2011-05-31 2012-12-06 St. Jude Medical Ab Dynamic cardiac resynchronization therapy by tracking inter -atrial conduction delays
DE102011078695A1 (en) * 2011-07-05 2013-01-10 Charité - Universitätsmedizin Berlin Dialysis procedure for removing protein-bound toxins from the blood of patients using high-frequency electromagnetic fields
JP5844467B2 (en) 2011-11-04 2016-01-20 カーディアック ペースメイカーズ, インコーポレイテッド Implantable medical device lead that includes a reverse wound inner coil with respect to the shock coil
US8600520B2 (en) 2012-04-18 2013-12-03 Pacesetter, Inc. Implantable lead assembly having a plurality of inductors
US8825179B2 (en) 2012-04-20 2014-09-02 Cardiac Pacemakers, Inc. Implantable medical device lead including a unifilar coiled cable
US8954168B2 (en) 2012-06-01 2015-02-10 Cardiac Pacemakers, Inc. Implantable device lead including a distal electrode assembly with a coiled component
US8958889B2 (en) 2012-08-31 2015-02-17 Cardiac Pacemakers, Inc. MRI compatible lead coil
JP6034499B2 (en) 2012-10-18 2016-11-30 カーディアック ペースメイカーズ, インコーポレイテッド Inductive element for providing MRI compatibility in implantable medical device leads
EP2835148A1 (en) 2013-08-04 2015-02-11 Greatbatch Ltd. Multilayer planar spiral inductor filter for medical, therapeutic or diagnostic applications
AU2015217286B2 (en) 2014-02-11 2016-12-22 Cardiac Pacemakers, Inc RF shield for an implantable lead
CN106029162A (en) 2014-02-26 2016-10-12 心脏起搏器股份公司 Construction of an MRI-safe tachycardia lead
US10183162B2 (en) 2015-01-02 2019-01-22 Greatbatch Ltd. Coiled, closed-loop RF current attenuator configured to be placed about an implantable lead conductor

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5398683A (en) * 1991-05-24 1995-03-21 Ep Technologies, Inc. Combination monophasic action potential/ablation catheter and high-performance filter system
US5964705A (en) * 1997-08-22 1999-10-12 Image-Guided Drug Delivery System, Inc. MR-compatible medical devices
WO1999060370A2 (en) * 1998-05-15 1999-11-25 Robin Medical, Inc. Method and apparatus for generating controlled torques
WO2000048512A1 (en) * 1999-02-22 2000-08-24 Cordis Corporation Magnetic resonance catheter for position tracking and imaging

Family Cites Families (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3871382A (en) * 1973-02-15 1975-03-18 Pacesetter Syst Heart stimulator system for rapid implantation and removal with improved integrity
US3968802A (en) * 1975-01-24 1976-07-13 Medtronic, Inc. Cautery protection circuit for a heart pacemaker
US4945912A (en) * 1988-11-25 1990-08-07 Sensor Electronics, Inc. Catheter with radiofrequency heating applicator
US5217010A (en) * 1991-05-28 1993-06-08 The Johns Hopkins University Ecg amplifier and cardiac pacemaker for use during magnetic resonance imaging
US5722998A (en) * 1995-06-07 1998-03-03 Intermedics, Inc. Apparatus and method for the control of an implantable medical device
US5697958A (en) * 1995-06-07 1997-12-16 Intermedics, Inc. Electromagnetic noise detector for implantable medical devices
US5629622A (en) * 1995-07-11 1997-05-13 Hewlett-Packard Company Magnetic field sense system for the protection of connected electronic devices
US6101417A (en) * 1998-05-12 2000-08-08 Pacesetter, Inc. Implantable electrical device incorporating a magnetoresistive magnetic field sensor
US6424234B1 (en) * 1998-09-18 2002-07-23 Greatbatch-Sierra, Inc. Electromagnetic interference (emi) filter and process for providing electromagnetic compatibility of an electronic device while in the presence of an electromagnetic emitter operating at the same frequency

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5398683A (en) * 1991-05-24 1995-03-21 Ep Technologies, Inc. Combination monophasic action potential/ablation catheter and high-performance filter system
US5964705A (en) * 1997-08-22 1999-10-12 Image-Guided Drug Delivery System, Inc. MR-compatible medical devices
WO1999060370A2 (en) * 1998-05-15 1999-11-25 Robin Medical, Inc. Method and apparatus for generating controlled torques
WO2000048512A1 (en) * 1999-02-22 2000-08-24 Cordis Corporation Magnetic resonance catheter for position tracking and imaging

Cited By (56)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9248283B2 (en) 2001-04-13 2016-02-02 Greatbatch Ltd. Band stop filter comprising an inductive component disposed in a lead wire in series with an electrode
US9295828B2 (en) 2001-04-13 2016-03-29 Greatbatch Ltd. Self-resonant inductor wound portion of an implantable lead for enhanced MRI compatibility of active implantable medical devices
US9302101B2 (en) 2004-03-30 2016-04-05 Medtronic, Inc. MRI-safe implantable lead
US7844343B2 (en) 2004-03-30 2010-11-30 Medtronic, Inc. MRI-safe implantable medical device
US9155877B2 (en) 2004-03-30 2015-10-13 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US7844344B2 (en) 2004-03-30 2010-11-30 Medtronic, Inc. MRI-safe implantable lead
US7877150B2 (en) 2004-03-30 2011-01-25 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US8989840B2 (en) 2004-03-30 2015-03-24 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US8886317B2 (en) 2004-12-17 2014-11-11 Cardiac Pacemakers, Inc. MRI operation modes for implantable medical devices
US8543207B2 (en) 2004-12-17 2013-09-24 Cardiac Pacemakers, Inc. MRI operation modes for implantable medical devices
US10084250B2 (en) 2005-02-01 2018-09-25 Medtronic, Inc. Extensible implantable medical lead
US8280526B2 (en) 2005-02-01 2012-10-02 Medtronic, Inc. Extensible implantable medical lead
US7853332B2 (en) 2005-04-29 2010-12-14 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US8027736B2 (en) 2005-04-29 2011-09-27 Medtronic, Inc. Lead electrode for use in an MRI-safe implantable medical device
US8897887B2 (en) 2006-06-08 2014-11-25 Greatbatch Ltd. Band stop filter employing a capacitor and an inductor tank circuit to enhance MRI compatibility of active medical devices
US10537730B2 (en) 2007-02-14 2020-01-21 Medtronic, Inc. Continuous conductive materials for electromagnetic shielding
US10398893B2 (en) 2007-02-14 2019-09-03 Medtronic, Inc. Discontinuous conductive filler polymer-matrix composites for electromagnetic shielding
US9044593B2 (en) 2007-02-14 2015-06-02 Medtronic, Inc. Discontinuous conductive filler polymer-matrix composites for electromagnetic shielding
US8483842B2 (en) 2007-04-25 2013-07-09 Medtronic, Inc. Lead or lead extension having a conductive body and conductive body contact
US9259572B2 (en) 2007-04-25 2016-02-16 Medtronic, Inc. Lead or lead extension having a conductive body and conductive body contact
US8554335B2 (en) 2007-12-06 2013-10-08 Cardiac Pacemakers, Inc. Method and apparatus for disconnecting the tip electrode during MRI
US8897875B2 (en) 2007-12-06 2014-11-25 Cardiac Pacemakers, Inc. Selectively connecting the tip electrode during therapy for MRI shielding
US9731119B2 (en) 2008-03-12 2017-08-15 Medtronic, Inc. System and method for implantable medical device lead shielding
US9108066B2 (en) 2008-03-20 2015-08-18 Greatbatch Ltd. Low impedance oxide resistant grounded capacitor for an AIMD
US8244375B2 (en) 2008-08-25 2012-08-14 Pacesetter, Inc. MRI compatible lead
US9561378B2 (en) 2008-10-02 2017-02-07 Cardiac Pacemakers, Inc. Implantable medical device responsive to MRI induced capture threshold changes
US8977356B2 (en) 2009-02-19 2015-03-10 Cardiac Pacemakers, Inc. Systems and methods for providing arrhythmia therapy in MRI environments
US10080889B2 (en) 2009-03-19 2018-09-25 Greatbatch Ltd. Low inductance and low resistance hermetically sealed filtered feedthrough for an AIMD
US9272136B2 (en) 2009-04-30 2016-03-01 Medtronic, Inc. Grounding of a shield within an implantable medical lead
US9220893B2 (en) 2009-04-30 2015-12-29 Medtronic, Inc. Shielded implantable medical lead with reduced torsional stiffness
US10035014B2 (en) 2009-04-30 2018-07-31 Medtronic, Inc. Steering an implantable medical lead via a rotational coupling to a stylet
US9216286B2 (en) 2009-04-30 2015-12-22 Medtronic, Inc. Shielded implantable medical lead with guarded termination
US9452284B2 (en) 2009-04-30 2016-09-27 Medtronic, Inc. Termination of a shield within an implantable medical lead
US10086194B2 (en) 2009-04-30 2018-10-02 Medtronic, Inc. Termination of a shield within an implantable medical lead
US9629998B2 (en) 2009-04-30 2017-04-25 Medtronics, Inc. Establishing continuity between a shield within an implantable medical lead and a shield within an implantable lead extension
US9205253B2 (en) 2009-04-30 2015-12-08 Medtronic, Inc. Shielding an implantable medical lead
US9186499B2 (en) 2009-04-30 2015-11-17 Medtronic, Inc. Grounding of a shield within an implantable medical lead
US9381371B2 (en) 2009-12-08 2016-07-05 Cardiac Pacemakers, Inc. Implantable medical device with automatic tachycardia detection and control in MRI environments
US8565874B2 (en) 2009-12-08 2013-10-22 Cardiac Pacemakers, Inc. Implantable medical device with automatic tachycardia detection and control in MRI environments
US10596369B2 (en) 2011-03-01 2020-03-24 Greatbatch Ltd. Low equivalent series resistance RF filter for an active implantable medical device
US11198014B2 (en) 2011-03-01 2021-12-14 Greatbatch Ltd. Hermetically sealed filtered feedthrough assembly having a capacitor with an oxide resistant electrical connection to an active implantable medical device housing
US11071858B2 (en) 2011-03-01 2021-07-27 Greatbatch Ltd. Hermetically sealed filtered feedthrough having platinum sealed directly to the insulator in a via hole
US10561837B2 (en) 2011-03-01 2020-02-18 Greatbatch Ltd. Low equivalent series resistance RF filter for an active implantable medical device utilizing a ceramic reinforced metal composite filled via
US9463317B2 (en) 2012-04-19 2016-10-11 Medtronic, Inc. Paired medical lead bodies with braided conductive shields having different physical parameter values
US9427596B2 (en) 2013-01-16 2016-08-30 Greatbatch Ltd. Low impedance oxide resistant grounded capacitor for an AIMD
USRE46699E1 (en) 2013-01-16 2018-02-06 Greatbatch Ltd. Low impedance oxide resistant grounded capacitor for an AIMD
US9931514B2 (en) 2013-06-30 2018-04-03 Greatbatch Ltd. Low impedance oxide resistant grounded capacitor for an AIMD
US10350421B2 (en) 2013-06-30 2019-07-16 Greatbatch Ltd. Metallurgically bonded gold pocket pad for grounding an EMI filter to a hermetic terminal for an active implantable medical device
US9993638B2 (en) 2013-12-14 2018-06-12 Medtronic, Inc. Devices, systems and methods to reduce coupling of a shield and a conductor within an implantable medical lead
US10279171B2 (en) 2014-07-23 2019-05-07 Medtronic, Inc. Methods of shielding implantable medical leads and implantable medical lead extensions
US10155111B2 (en) 2014-07-24 2018-12-18 Medtronic, Inc. Methods of shielding implantable medical leads and implantable medical lead extensions
US10589107B2 (en) 2016-11-08 2020-03-17 Greatbatch Ltd. Circuit board mounted filtered feedthrough assembly having a composite conductive lead for an AIMD
US10559409B2 (en) 2017-01-06 2020-02-11 Greatbatch Ltd. Process for manufacturing a leadless feedthrough for an active implantable medical device
US10905888B2 (en) 2018-03-22 2021-02-02 Greatbatch Ltd. Electrical connection for an AIMD EMI filter utilizing an anisotropic conductive layer
US10912945B2 (en) 2018-03-22 2021-02-09 Greatbatch Ltd. Hermetic terminal for an active implantable medical device having a feedthrough capacitor partially overhanging a ferrule for high effective capacitance area
US11712571B2 (en) 2018-03-22 2023-08-01 Greatbatch Ltd. Electrical connection for a hermetic terminal for an active implantable medical device utilizing a ferrule pocket

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