US20030144720A1 - Electromagnetic trap for a lead - Google Patents

Electromagnetic trap for a lead Download PDF

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Publication number
US20030144720A1
US20030144720A1 US10/059,598 US5959802A US2003144720A1 US 20030144720 A1 US20030144720 A1 US 20030144720A1 US 5959802 A US5959802 A US 5959802A US 2003144720 A1 US2003144720 A1 US 2003144720A1
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United States
Prior art keywords
coil
electrical lead
medical electrical
impedance
presence
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Abandoned
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US10/059,598
Inventor
Eduardo Villaseca
Garry Dublin
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Medtronic Inc
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Medtronic Inc
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Priority to US10/059,598 priority Critical patent/US20030144720A1/en
Assigned to MEDTRONIC, INC. reassignment MEDTRONIC, INC. ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: VILLASECA, EDUARDO H., DUBLIN, GARRY L.
Priority claimed from EP03707558A external-priority patent/EP1469910B1/en
Publication of US20030144720A1 publication Critical patent/US20030144720A1/en
Application status is Abandoned legal-status Critical

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    • 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

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

    FIELD OF THE INVENTION
  • 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. [0001]
  • DESCRIPTION OF THE RELATED ART
  • 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. [0002]
  • 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). [0003]
  • 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. [0004]
  • 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. [0005]
  • 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. [0006]
  • 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. [0007]
  • 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. [0008]
  • The present invention is directed to overcoming, or at least reducing the effects of, one or more of the problems set forth above. [0009]
  • 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. [0010]
  • 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. [0011]
  • 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.[0012]
  • 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: [0013]
  • FIG. 1 is a simplified diagram of an implementation of an implantable medical device, in accordance with one illustrative embodiment of the present invention; [0014]
  • FIG. 2 illustrates a simplified block diagram representation of an implantable medical system in accordance with one illustrative embodiment of the present invention; [0015]
  • FIG. 3 illustrates a stylized depiction of a lead used in the implantable medical system, in accordance with one embodiment of the present invention; [0016]
  • FIG. 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; [0017]
  • FIG. 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; [0018]
  • FIG. 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 [0019]
  • FIGS. 7[0020] a, 7 b, 7 c, and 7 d 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. [0021]
  • 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. [0022]
  • 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. [0023]
  • 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. [0024]
  • Turning now to FIG. 1, one embodiment of implementing an implantable medical device into a human body is illustrated. A sensor/therapy delivery device [0025] 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 [0026] 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 FIG. 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 FIG. 2, a system [0027] 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 FIG. 3, a medical electrical lead [0028] 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 FIG. 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 electromagnetic fields, such as fields present during an MRI processes, a substantial amount of RF signal-induced current may be present around the tip [0029] 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 FIG. 4, a coil [0030] 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 FIG. 5, an enlarged view of the distal end [0031] 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 [0032] 410 is made up of a wire that is insulated. Turning now to FIG. 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 FIGS. [0033] 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 FIG. 7A. 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 [0034] 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 [0035] 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 FIG. 7B, an alternative embodiment of the equivalent circuit provided by the coil [0036] 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 [0037] 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 [0038] 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 FIG. 7C, at low frequencies, the low-frequency current (I[0039] low freq) 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 FIGS. 7C and 7D).
  • At high frequencies, the current induced by RF signals (I[0040] high 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 FIG. 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 [0041] 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. [0042]

Claims (22)

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.
US10/059,598 2002-01-29 2002-01-29 Electromagnetic trap for a lead Abandoned US20030144720A1 (en)

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US10/059,598 US20030144720A1 (en) 2002-01-29 2002-01-29 Electromagnetic trap for a lead

Applications Claiming Priority (8)

Application Number Priority Date Filing Date Title
US10/059,598 US20030144720A1 (en) 2002-01-29 2002-01-29 Electromagnetic trap for a lead
US10/136,798 US7013180B2 (en) 2002-01-29 2002-04-30 Conditioning of coupled electromagnetic signals on a lead
EP03707558A EP1469910B1 (en) 2002-01-29 2003-01-27 Conditioning of coupled electromagnetic signals on a lead
PCT/US2003/002435 WO2003063954A1 (en) 2002-01-29 2003-01-27 Conditioning of coupled electromagnetic signals on a lead
PCT/US2003/002436 WO2003063955A1 (en) 2002-01-29 2003-01-27 Electromagnetic trap for a lead
CA002472264A CA2472264A1 (en) 2002-01-29 2003-01-27 Conditioning of coupled electromagnetic signals on a lead
DE60310194T DE60310194T2 (en) 2002-01-29 2003-01-27 Filtering of coupled electromagnetic signals on supplies
JP2003563639A JP4326340B2 (en) 2002-01-29 2003-01-27 Medical electrical leads

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US10/136,798 Continuation-In-Part US7013180B2 (en) 2002-01-29 2002-04-30 Conditioning of coupled electromagnetic signals on a lead

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