MRI compatible electrical lead for an implanted electronic medical device

• US 8,285,396 B2
• Filed: 01/04/2010
• Issued: 10/09/2012
• Est. Priority Date: 01/05/2009
• Status: Expired due to Fees

• Current Assignee: Kenergy, Inc.
• Original Assignee: Kenergy, Inc.
• Inventors: Bulkes, Cherik, Denker, Stephen
• Primary Examiner(s): Layno, Carl H
• Assistant Examiner(s): Stice, Paula J
• Application Number:
  US12/651,597
• Publication Number:
  US 20100174348A1
• Time in Patent Office: 1,009 Days
• Field of Search: 607/2, 607115-119
• US Class Current: 607/116
• CPC Class Codes: A61N 1/05 for implantation or insertion into the body, e.g. heart electrode A61N1/06 takes precedence
• CPC Class Codes: A61N 1/086 Magnetic resonance imaging [MRI] compatible leads
• CPC Class Codes: A61N 1/3718 Monitoring of or protection against external electromagnetic fields or currents

Abstract

An electrical lead, for implantation in an animal, is compatible with an MRI scanner. The electrical lead has a first plurality of coiled insulated wires forming an outer layer of conductors that has a first inductance and a first capacitance, which act as a first parallel resonator tuned to a Larmor frequency of tissue in the animal. The lead may have a second plurality of coiled insulated wires forming an inner layer of conductors within the outer layer of conductors. The second plurality of coiled insulated wires has a second inductance and a second capacitance that act as a second parallel resonator tuned to the Larmor frequency. Those parallel resonators mitigate signals at the Larmor frequency from traveling along the respective coil. An electrically conductive layer extends around the inner and/or outer layer of conductors, and a layer of a biologically compatible material forms the electrical lead'"'"'s exterior surface.

Claims

1. An electrical lead that is adapted for implantation in an animal and compatible with a magnetic resonance imaging scanner, wherein the magnetic resonance imaging scanner responds to signals at a Larmor frequency of tissue in the animal, said electrical lead comprising:

a first coil including at least one first insulated conductor wound along a length of the lead in a physical manner that defines a first inductance and a first capacitance of the first coil, wherein the first inductance and the first capacitance are configured to cause the first coil to act as a first parallel resonator tuned to the Larmor frequency;

an electrically conductive layer extending around the first coil; and

a layer of a material that is electrically insulating and biologically compatible with tissue of the animal, and which forms an external surface of the electrical lead.

2. The electrical lead as recited in claim 1 wherein the first coil comprises a plurality of coiled insulated conductors.

3. The electrical lead as recited in claim 1 wherein the electrically conductive layer contains electrically conductive, non-magnetizable particles in physical contact with each other.

4. The electrical lead as recited in claim 1 wherein the Larmor frequency is one of 64 MHz and 128 MHz.

5. The electrical lead as recited in claim 1 wherein the first coil has the length which is unequal to a multiple of half a wavelength of the Larmor frequency.

6. The electrical lead as recited in claim 1 wherein the at least one first insulated conductor has a conductivity between 1.00 and 2×

10⁵ Siemens per meter.

7. The electrical lead as recited in claim 1 further comprising a second coil including at least one second insulated conductor wound along the length of the lead and around the first coil in a physical manner that defines a second inductance and a second capacitance, wherein the second inductance and the second capacitance are configured to cause the second coil to act as a second parallel resonator that resonates at the Larmor frequency.

8. The electrical lead as recited in claim 7 wherein the electrically conductive layer is between the first coil and the second coil.

9. The electrical lead as recited in claim 8 wherein the electrically conductive layer further encases the second coil.

10. The electrical lead as recited in claim 7 wherein the second coil is between the first coil and the electrically conductive layer.

11. The electrical lead as recited in claim 10 further comprising a spacer layer of dielectric material between the first coil and the second coil.

12. The electrical lead as recited in claim 10 further comprising a spacer layer of electrically conductive material between the first coil and the second coil.

13. The electrical lead as recited in claim 7 wherein the first coil and the second coil are wound in identical directions along the length of the lead.

14. The electrical lead as recited in claim 7 wherein the first coil and the second coil are wound in opposite directions along a length of the lead.

15. The electrical lead as recited in claim 7 wherein the first coil and the second coil each comprises a plurality of coiled insulated conductors.

16. The electrical lead as recited in claim 1 wherein the first inductance L is defined by the expression L=μ

μ

₀m²Al, where μ

is the magnetic permeability of air, μ

₀ is the magnetic permeability of a vacuum, m is the number of turns per unit length of the coil, A is a cross sectional area of the coil, and l is the length of the coil.

17. An electrical lead that is adapted for implantation in an animal and compatible with a magnetic resonance imaging scanner which responds to signals at a Larmor frequency of tissue in the animal, said electrical lead comprising:

a first plurality of coiled insulated wires wound in a first direction forming an outer layer of conductors, and having a first pitch that produces a first inductance and a first capacitance, wherein the first inductance and the first capacitance are configured to cause the first coil to act as a first parallel resonator tuned to the Larmor frequency;

a second plurality of coiled insulated wires wound in a second direction forming an inner layer of conductors within the outer layer of conductors, and having a second pitch that produces a second inductance and a second capacitance, wherein the second inductance and the second capacitance are configured to cause the first coil to act as a second parallel resonator tuned to the Larmor frequency;

an electrically conductive layer extends around the inner layer of conductors; and

a layer of a material that is biologically compatible with tissue of the animal and extending around the outer layer of conductors and the electrically conductive layer.

18. The electrical lead as recited in claim 17 wherein the electrically conductive layer contains electrically conductive, non-magnetizable particles in physical contact with each other.

19. The electrical lead as recited in claim 17 wherein each of the first plurality of coiled insulated wires and the second plurality of coiled insulated wires has a conductivity between 1.00 and 2×

10⁵ Siemens per meter.

20. The electrical lead as recited in claim 17 wherein the electrically conductive layer is around the outer layer of conductors.

21. The electrical lead as recited in claim 20 further comprising a spacer layer of dielectric material between the inner layer of conductors and the outer layer of conductors.

22. The electrical lead as recited in claim 20 further comprising a spacer layer of electrically conductive material between the inner layer of conductors and the outer layer of conductors.

23. The electrical lead as recited in claim 17 wherein the electrically conductive layer is between the inner layer of conductors and the outer layer of conductors.

24. The electrical lead as recited in claim 17 wherein the first direction and the second direction are identical.

25. The electrical lead as recited in claim 17 wherein the first direction is opposite to the second direction.

26. The electrical lead as recited in claim 17 wherein the coil has a length which is unequal to a multiple of half a wavelength of the Larmor frequency.

27. The electrical lead as recited in claim 17 wherein the first inductance L is defined by the expression L=μ

μ

₀m²Al, where μ

is the magnetic permeability of air, μ

₀ is the magnetic permeability of a vacuum, m is the number of turns per unit length of the coil, A is the cross sectional area of the coil, and l is the length of the coil.