US20050182471A1 - Magnetically shielded conductor - Google Patents
Magnetically shielded conductor Download PDFInfo
- Publication number
- US20050182471A1 US20050182471A1 US11/085,415 US8541505A US2005182471A1 US 20050182471 A1 US20050182471 A1 US 20050182471A1 US 8541505 A US8541505 A US 8541505A US 2005182471 A1 US2005182471 A1 US 2005182471A1
- Authority
- US
- United States
- Prior art keywords
- recited
- magnetically shielded
- conductor assembly
- conductor
- shielded conductor
- Prior art date
- Legal status (The legal status 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 status listed.)
- Abandoned
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/362—Heart stimulators
- A61N1/37—Monitoring; Protecting
- A61N1/3718—Monitoring of or protection against external electromagnetic fields or currents
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B82—NANOTECHNOLOGY
- B82Y—SPECIFIC USES OR APPLICATIONS OF NANOSTRUCTURES; MEASUREMENT OR ANALYSIS OF NANOSTRUCTURES; MANUFACTURE OR TREATMENT OF NANOSTRUCTURES
- B82Y25/00—Nanomagnetism, e.g. magnetoimpedance, anisotropic magnetoresistance, giant magnetoresistance or tunneling magnetoresistance
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01B—CABLES; CONDUCTORS; INSULATORS; SELECTION OF MATERIALS FOR THEIR CONDUCTIVE, INSULATING OR DIELECTRIC PROPERTIES
- H01B11/00—Communication cables or conductors
- H01B11/02—Cables with twisted pairs or quads
- H01B11/06—Cables with twisted pairs or quads with means for reducing effects of electromagnetic or electrostatic disturbances, e.g. screens
- H01B11/10—Screens specially adapted for reducing interference from external sources
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01B—CABLES; CONDUCTORS; INSULATORS; SELECTION OF MATERIALS FOR THEIR CONDUCTIVE, INSULATING OR DIELECTRIC PROPERTIES
- H01B11/00—Communication cables or conductors
- H01B11/02—Cables with twisted pairs or quads
- H01B11/06—Cables with twisted pairs or quads with means for reducing effects of electromagnetic or electrostatic disturbances, e.g. screens
- H01B11/10—Screens specially adapted for reducing interference from external sources
- H01B11/1058—Screens specially adapted for reducing interference from external sources using a coating, e.g. a loaded polymer, ink or print
- H01B11/1083—Screens specially adapted for reducing interference from external sources using a coating, e.g. a loaded polymer, ink or print the coating containing magnetic material
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01F—MAGNETS; INDUCTANCES; TRANSFORMERS; SELECTION OF MATERIALS FOR THEIR MAGNETIC PROPERTIES
- H01F1/00—Magnets or magnetic bodies characterised by the magnetic materials therefor; Selection of materials for their magnetic properties
- H01F1/0036—Magnets or magnetic bodies characterised by the magnetic materials therefor; Selection of materials for their magnetic properties showing low dimensional magnetism, i.e. spin rearrangements due to a restriction of dimensions, e.g. showing giant magnetoresistivity
- H01F1/0045—Zero dimensional, e.g. nanoparticles, soft nanoparticles for medical/biological use
- H01F1/0063—Zero dimensional, e.g. nanoparticles, soft nanoparticles for medical/biological use in a non-magnetic matrix, e.g. granular solids
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01F—MAGNETS; INDUCTANCES; TRANSFORMERS; SELECTION OF MATERIALS FOR THEIR MAGNETIC PROPERTIES
- H01F10/00—Thin magnetic films, e.g. of one-domain structure
- H01F10/007—Thin magnetic films, e.g. of one-domain structure ultrathin or granular films
-
- H—ELECTRICITY
- H01—ELECTRIC ELEMENTS
- H01F—MAGNETS; INDUCTANCES; TRANSFORMERS; SELECTION OF MATERIALS FOR THEIR MAGNETIC PROPERTIES
- H01F10/00—Thin magnetic films, e.g. of one-domain structure
- H01F10/32—Spin-exchange-coupled multilayers, e.g. nanostructured superlattices
- H01F10/324—Exchange coupling of magnetic film pairs via a very thin non-magnetic spacer, e.g. by exchange with conduction electrons of the spacer
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/02—Details
- A61N1/08—Arrangements or circuits for monitoring, protecting, controlling or indicating
- A61N1/086—Magnetic resonance imaging [MRI] compatible leads
Definitions
- a conductor assembly comprised of a conductor disposed within an insulating sheath, wherein the sheath is coated with nanomagnetic material and nanoelectrical material.
- implantable devices such as implantable pulse generators (IPGs) and cardioverter/defibrillator/pacemaker (CDPs), are sensitive to a variety of forms of electromagnetic interference (EMI). These devices include sensing and logic systems that respond to low-level signals from the heart. Because the sensing systems and conductive elements of these implantable devices are responsive to changes in local electromagnetic fields, they are vulnerable to external sources of severe electromagnetic noise, and in particular to electromagnetic fields emitted during magnetic resonance imaging (MRI) procedures. Therefore, patients with implantable devices are generally advised not to undergo magnetic resonance imaging (MRI) procedures, which often generate magnetic fields of from between about 1 about 20 Teslas.
- MRI magnetic resonance imaging
- a magnetically shielded conductor assembly comprised of a conductor disposed within an insulating matrix, wherein said insulating matrix is coated with a nanomagnetic particulate material.
- FIG. 1 is a schematic sectional view of a shielded implanted device comprised of one preferred conductor assembly of the invention
- FIG. 1A is a flow diagram of a preferred process of the invention
- FIG. 2 is an enlarged sectional view of a portion of the conductor assembly of FIG. 1 ;
- FIG. 3 is a sectional view of another conductor assembly of this invention.
- FIG. 4 is a schematic view of the conductor assembly of FIG. 2 ;
- FIG. 5 is a sectional view of the conductor assembly of FIG. 2 ;
- FIGS. 6A and 6B are side and end sectional views of another preferred conductor assembly of this invention.
- FIGS. 7A and 7B are end and side sectional views of yet another preferred conductor assembly of this invention.
- FIG. 8 is a schematic representation of a conductor assembly that is partially coated and partially uncoated.
- FIG. 1 is a schematic sectional view of one preferred device 10 that, in one embodiment, is implanted in a living organism.
- device 10 is comprised of a power source 12 , a first conductor 14 , a second conductor 16 , a first insulative shield 18 disposed about power source 12 , a second insulative shield 20 disposed about a load 22 , a third insulative shield 23 disposed about a first conductor 14 , and a second conductor 16 , and a multiplicity of nanomagnetic particles 24 disposed on said first insulative shield, said second insulative shield, and said third insulative shield.
- the power source 12 is a battery 12 that is operatively connected to a controller 26 .
- controller 26 is operatively connected to the load 22 and the switch 28 . Depending upon the information furnished to controller 26 , it may deliver no current, direct current, and/or current pulses to the load 22 .
- the controller 26 and/or the wires 30 and 32 are shielded from magnetic radiation.
- one or more connections between the controller 26 and the switch 28 and/or the load 22 are made by wireless means such as, e.g., telemetry means.
- the power source 12 provides a source of alternating current. In another embodiment, the power source 12 in conjunction with the controller 26 provides pulsed direct current.
- the load 22 may be any of the implanted devices known to those skilled in the art.
- load 22 may be a pacemaker.
- load 22 may be an artificial heart.
- load 22 may be a heart-massaging device.
- load 22 may be a defibrillator.
- the conductors 14 and 16 may be any conductive material(s) that have a resistivity at 20 degrees Centigrade of from about 1 to about 100 microohm-centimeters.
- the conductive material(s) may be silver, copper, aluminum, alloys thereof, mixtures thereof, and the like.
- the conductors 14 and 16 consist essentially of such conductive material.
- step 40 the conductive wires 14 and 16 are coated with electrically insulative material.
- Suitable insulative materials include nano-sized silicon dioxide, aluminum oxide, cerium oxide, yttrium-stabilized zirconia, silicon carbide, silicon nitride, aluminum nitride, and the like. In general, these nano-sized particles will have a particle size distribution such that at least about 90 weight percent of the particles have a maximum dimension in the range of from about 10 to about 100 nanometers.
- the coated conductors 14 and 16 may be prepared by conventional means such as, e.g., the process described in U.S. Pat. No. 5,540,959, the entire disclosure of which is hereby incorporated by reference into this specification.
- This patent describes and claims a process for preparing a coated substrate, comprising the steps of: (a) creating mist particles from a liquid, wherein: 1. said liquid is selected from the group consisting of a solution, a slurry, and mixtures thereof, 2. said liquid is comprised of solvent and from 0.1 to 75 grams of solid material per liter of solvent, 3. at least 95 volume percent of said mist particles have a maximum dimension less than 100 microns, and 4.
- said mist particles are created from said first liquid at a rate of from 0.1 to 30 milliliters of liquid per minute; (b) contacting said mist particles with a carrier gas at a pressure of from 761 to 810 millimeters of mercury; (c) thereafter contacting said mist particles with alternating current radio frequency energy with a frequency of at least 1 megahertz and a power of at least 3 kilowatts while heating said mist particles to a temperature of at least about 100 degrees centigrade, thereby producing a heated vapor; (d) depositing said heated vapor onto a substrate, thereby producing a coated substrate; and (e) subjecting said coated substrate to a temperature of from about 450 to about 1,400 degrees centigrade for at least about 10 minutes.
- conductors 14 and 16 may be coated by means of the processes disclosed in a text by D. Satas on “Coatings Technology Handbook” (Marcel Dekker, Inc., New York, N.Y., 1991). As is disclosed in such text, one may use cathodic arc plasma deposition (see pages 229 et seq.), chemical vapor deposition (see pages 257 et seq.), sol-gel coatings (see pages 655 et seq.), and the like.
- FIG. 2 is a sectional view of the coated conductors 14 / 16 of the device of FIG. 1 .
- conductors 14 and 16 are separated by insulating material 42 .
- the insulating material 42 that is disposed between conductors 14 / 16 may be the same as the insulating material 44 / 46 that is disposed above conductor 14 and below conductor 16 .
- the insulating material 42 may be different from the insulating material 44 and/or the insulating material 46 .
- step 48 of the process describes disposing insulating material between the coated conductors 14 and 16 . This step may be done simultaneously with step 40 ; and it may be done thereafter.
- the insulating material 42 , the insulating material 44 , and the insulating material 46 each generally has a resistivity of from about 1 ⁇ 10 9 to about 1 ⁇ 10 13 ohm-centimeters.
- the coated conductor assembly is preferably heat treated in step 50 .
- This heat treatment often is used in conjunction with coating processes in which the heat is required to bond the insulative material to the conductors 14 / 16 .
- the heat-treatment step may be conducted after the deposition of the insulating material 42 / 44 / 46 , or it may be conducted simultaneously therewith. In either event, and when it is used, it is preferred to heat the coated conductors 14 / 16 to a temperature of from about 200 to about 600 degrees Centigrade for from about 1 minute to about 10 minutes.
- step 52 of the process after the coated conductors 14 / 16 have been subjected to heat treatment step 50 , they are allowed to cool to a temperature of from about 30 to about 100 degrees Centigrade over a period of time of from about 3 to about 15 minutes.
- nanomagnetic materials are coated onto the previously coated conductors 14 and 16 . This is best shown in FIG. 2 , wherein the nanomagnetic particles are identified as particles 24 .
- nanomagnetic material is magnetic material which has an average particle size less than 100 nanometers and, preferably, in the range of from about 2 to 50 nanometers. Reference may be had, e.g., to U.S. Pat. No. 5,889,091 (rotationally free nanomagnetic material), U.S. Pat. Nos. 5,714,536, 5,667,924, and the like. The entire disclosure of each of these United States patents is hereby incorporated by reference into this specification.
- the nanomagnetic materials may be, e.g., nano-sized ferrites such as, e.g., the nanomagnetic ferrites disclosed in U.S. Pat. No. 5,213,851, the entire disclosure of which is hereby incorporated by reference into this specification.
- This patent claims a process for coating a layer of ferritic material with a thickness of from about 0.1 to about 500 microns onto a substrate at a deposition rate of from about 0.01 to about 10 microns per minute per 35 square centimeters of substrate surface, comprising the steps of: (a) providing a solution comprised of a first compound and a second compound, wherein said first compound is an iron compound and said second compound is selected from the group consisting of compounds of nickel, zinc, magnesium, strontium, barium, manganese, lithium, lanthanum, yttrium, scandium, samarium, europium, terbium, dysprosium, holmium, erbium, ytterbium, lutetium, cerium, praseodymium, thulium, neodymium, gadolinium, aluminum, iridium, lead, chromium, gallium, indium, chromium, samarium, cobalt, titanium, and
- the thickness of the layer of nanomagnetic material deposited onto the coated conductors 14 / 16 is less than about 5 microns and generally from about 0.1 to about 3 microns.
- the coated assembly may be optionally heat-treated in step 56 .
- this optional step 56 it is preferred to subject the coated conductors 14 / 16 to a temperature of from about 200 to about 600 degrees Centigrade for from about I to about 10 minutes.
- one or more additional insulating layers 43 are coated onto the assembly depicted in FIG. 2 , by one or more of the processes disclosed hereinabove. This is conducted in optional step 58 (see FIG. IA).
- FIG. 4 is a partial schematic view of the assembly 11 of FIG. 2 , illustrating the current flow in such assembly. Referring go FIG. 4 , it will be seen that current flows into conductor 14 in the direction of arrow 60 , and it flows out of conductor 16 in the direction of arrow 62 . The net current flow through the assembly 11 is zero; and the net Lorentz force in the assembly 11 is thus zero. Consequently, even high current flows in the assembly 11 do not cause such assembly to move.
- conductors 14 and 16 are substantially parallel to each other. As will be apparent, without such parallel orientation, there may be some net current and some net Lorentz effect.
- the conductors 14 and 16 preferably have the same diameters and/or the same compositions and/or the same length.
- the nanomagnetic particles 24 are present in a density sufficient so as to provide shielding from magnetic flux lines 64 . Without wishing to be bound to any particular theory, applicant believes that the nanomagnetic particles 24 trap and pin the magnetic lines of flux 64 .
- the nanomagnetic particles 24 have a specified magnetization.
- magnetization is the magnetic moment per unit volume of a substance. Reference may be had, e.g., to U.S. Pat. Nos. 4,169,998, 4,168,481, 4,166,263, 5,260,132, 4,778,714, and the like. The entire disclosure of each of these United States patents is hereby incorporated by reference into this specification.
- the layer of nanomagnetic particles 24 preferably has a saturation magnetization, at 25 degrees Centigrade, of from about 200 to about 25,000 Gauss, or higher.
- the saturation magnetization at room temperature of the nanomagnetic particles is from about 500 to about 10,000 Gauss.
- a thin film with a thickness of less than about 2 microns and a saturation magnetization in excess of 20,000 Gauss.
- the thickness of the layer of nanomagnetic material is measured from the bottom surface of the layer that contains such material to the top surface of such layer that contains such material; and such bottom surface and/or such top surface may be contiguous with other layers of material (such as insulating material) that do not contain nanomagnetic particles.
- a saturation magnetization of 24,000 Gauss By the appropriate selection of nanomagnetic particles, and the thickness of the films deposited, one may obtain saturation magnetizations of as high as at least about 26,000.
- the nanomagnetic particles 24 are disposed within an insulating matrix so that any heat produced by such particles will be slowly dispersed within such matrix.
- Such matrix may be made from ceria, calcium oxide, silica, alumina.
- the insulating material 42 preferably has a thermal conductivity of less than about 20 (calories centimeters/square centimeters-degree second) ⁇ 10,000. See, e.g., page E-6 of the 63 rd Edition of the “Handbook of Chemistry and Physics” (CRC Press, Inc., Boca Raton, Fla., 1982).
- the nanomagnetic materials 24 typically comprise one or more of iron, cobalt, nickel, gadolinium, and samarium atoms.
- typical nanomagnetic materials include alloys of iron and nickel (permalloy), cobalt, niobium, and zirconium (CNZ), iron, boron, and nitrogen, cobalt, iron, boron, and silica, iron, cobalt, boron, and fluoride, and the like.
- FIG. 5 is a sectional view of the assembly 11 of FIG. 2 .
- the device of FIG. 5 and of the other Figures of this application, is preferably substantially flexible.
- the term flexible refers to an assembly that can be bent to form a circle with a radius of less than 2 centimeters without breaking. Put another way, the bend radius of the coated assembly 11 can be less than 2 centimeters.
- FIGS. 6A and 6B are side and end sectional views of another preferred conductor assembly 101 of this invention.
- the assembly 101 is similar in configuration to the assembly 11 but differs therefrom in that only one conductor 14 is utilized. Disposed around conductor 14 are a layer of insulating material 44 , a layer of nanoelectrical material 102 , and a layer of nanomagnetic material 100 .
- the layer of nanoelectrical material 102 preferably has a thickness of from about 0.5 to about 2 microns.
- the nanoelectrical material comprising layer 102 has a resistivity of from about 1.6 to about 100 microohm-centimeters.
- WO9820719 in which reference is made to U.S. Pat. No. 4,963,291; each of these patents and patent applications is hereby incorporated by reference into this specification.
- the nanoelectrical particles used in this invention preferably have a particle size within the range of from about I to about 100 microns, and a resistivity of from about 1.6 to about 100 microohm-centimeters.
- such nanoelectrical particles comprise a mixture of iron and aluminum.
- such nanoelectrical particles consist essentially of a mixture of iron and aluminum. It is preferred that, in such nanoelectrical particles, and in one embodiment, at least 9 moles of aluminum are present for each mole of iron. In another embodiment, at least about 9.5 moles of aluminum are present for each mole of iron. In yet another embodiment, at least 9.9 moles of aluminum are present for each mole of iron.
- FIGS. 7A and 7B are end and side sectional views of conductor assembly 120 that is similar to the assembly 101 (see FIGS. 6A and 6B ) but differs therefrom in that the nanoelectrical material and the nanomagnetic material are both disposed in the same layer 105 .
- FIG. 8 is schematic representation of a coated conductor assembly 130 comprised of flexible conductor 14 and coating 105 .
- the coating 105 contains both nanomagnetic and nanoelectrical particles. In another embodiment, not shown, the coating 105 contains only nanomagnetic particles.
- sections 134 , 134 , and 136 , and 138 are not coated with the coating 105 .
- the uncoated sections 134 et seq. are less likely to increase their temperature upon being exposed to electromagnetic radiation and, thus, can more readily be contacted with the tissue of a biological organism.
Abstract
A magnetically shielded conductor assembly containing a conductor disposed within an insulating matrix, and nanomagnetic material and nanoelectrical material disposed around the conductor. The conductor has a resistivity at 20 degrees Centigrade of from about 1 to about 100 microohm-centimeters. The insulating matrix is composed of nano-sized particles having a maximum dimension of from about 10 to about 100 nanometers. The insulating matrix has a resistivity of from about 1×109 to about 1×10 13 ohm-centimeter. The nanomagnetic material has an average particle size of less than about 100 nanometers. The nanomagnetic material has a saturation magnetization of from about 200 to about 26,000 Gauss. The magnetically shielded conductor assembly is flexible, having a bend radius of less than 2 centimeters.
Description
- This application is a continuation of applicant's co-pending patent application, U.S. Ser. No. 10/229,183, filed on Aug. 26, 2002, which is a continuation-in-part of U.S. Ser. No. 10/054,407, filed on Jan. 22, 2002. The entire content of each of the above patent applications is hereby incorporated by reference into this specification.
- A conductor assembly comprised of a conductor disposed within an insulating sheath, wherein the sheath is coated with nanomagnetic material and nanoelectrical material.
- Many implanted medical devices that are powered by electrical energy have been developed. Most of these devices comprise a power source, one or more conductors, and a load.
- When a patient with one of these implanted devices is subjected to high intensity magnetic fields, currents are often induced in the implanted conductors. The large current flows so induced often create substantial amounts of heat. Because living organisms can generally only survive within a relatively narrow range of temperatures, these large current flows are dangerous.
- Furthermore, implantable devices, such as implantable pulse generators (IPGs) and cardioverter/defibrillator/pacemaker (CDPs), are sensitive to a variety of forms of electromagnetic interference (EMI). These devices include sensing and logic systems that respond to low-level signals from the heart. Because the sensing systems and conductive elements of these implantable devices are responsive to changes in local electromagnetic fields, they are vulnerable to external sources of severe electromagnetic noise, and in particular to electromagnetic fields emitted during magnetic resonance imaging (MRI) procedures. Therefore, patients with implantable devices are generally advised not to undergo magnetic resonance imaging (MRI) procedures, which often generate magnetic fields of from between about 1 about 20 Teslas.
- One additional problem with implanted conductors is that, when they are conducting electricity and are simultaneously subjected to large magnetic fields, a Lorentz force is created which often causes the conductor to move. This movement may damage body tissue.
- In U.S. Pat. No. 4,180,600, there is disclosed and claimed a fine magnetically shielded conductor wire consisting of a conductive copper core and a magnetically soft alloy metallic sheath metallurgically secured to the conductive core, wherein the sheath consists essentially of from 2 to 5 weight percent of molybdenum, from about 15 to about 23 weight percent of iron, and from about 75 to about 85 weight percent of nickel. Although the device of this patent does provide magnetic shielding, it still creates heat when it interacts with strong magnetic fields.
- It is an object of this invention to provide a conductor assembly, which is shielded from large magnetic fields, which does not create large amounts of heat in the presence of such fields, and which does not exhibit the Lorentz effect when subjected to such fields.
- In accordance with this invention, there is provided a magnetically shielded conductor assembly comprised of a conductor disposed within an insulating matrix, wherein said insulating matrix is coated with a nanomagnetic particulate material.
- The invention will be described by reference to the following drawings, in which like numerals refer to like elements, and in which:
-
FIG. 1 is a schematic sectional view of a shielded implanted device comprised of one preferred conductor assembly of the invention; -
FIG. 1A is a flow diagram of a preferred process of the invention; -
FIG. 2 is an enlarged sectional view of a portion of the conductor assembly ofFIG. 1 ; -
FIG. 3 is a sectional view of another conductor assembly of this invention; -
FIG. 4 is a schematic view of the conductor assembly ofFIG. 2 ; -
FIG. 5 is a sectional view of the conductor assembly ofFIG. 2 ; -
FIGS. 6A and 6B are side and end sectional views of another preferred conductor assembly of this invention; -
FIGS. 7A and 7B are end and side sectional views of yet another preferred conductor assembly of this invention; and -
FIG. 8 is a schematic representation of a conductor assembly that is partially coated and partially uncoated. -
FIG. 1 is a schematic sectional view of onepreferred device 10 that, in one embodiment, is implanted in a living organism. Referring toFIG. 1 , it will be seen thatdevice 10 is comprised of apower source 12, afirst conductor 14, asecond conductor 16, a firstinsulative shield 18 disposed aboutpower source 12, a secondinsulative shield 20 disposed about aload 22, a thirdinsulative shield 23 disposed about afirst conductor 14, and asecond conductor 16, and a multiplicity ofnanomagnetic particles 24 disposed on said first insulative shield, said second insulative shield, and said third insulative shield. - In the embodiment depicted in
FIG. 1 , thepower source 12 is abattery 12 that is operatively connected to acontroller 26. In the embodiment depicted,controller 26 is operatively connected to theload 22 and theswitch 28. Depending upon the information furnished to controller 26, it may deliver no current, direct current, and/or current pulses to theload 22. - In one embodiment, not shown, the
controller 26 and/or thewires controller 26 and theswitch 28 and/or theload 22 are made by wireless means such as, e.g., telemetry means. - In one embodiment, not shown, the
power source 12 provides a source of alternating current. In another embodiment, thepower source 12 in conjunction with thecontroller 26 provides pulsed direct current. - The
load 22 may be any of the implanted devices known to those skilled in the art. Thus, e.g.,load 22 may be a pacemaker. Thus, e.g.,load 22 may be an artificial heart. Thus, e.g.,load 22 may be a heart-massaging device. Thus, e.g.,load 22 may be a defibrillator. - The
conductors conductors - In the first step of the process of this invention,
step 40, theconductive wires - The coated
conductors - By way of further illustration, one may
coat conductors -
FIG. 2 is a sectional view of thecoated conductors 14/16 of the device ofFIG. 1 . Referring toFIG. 2 , it will be seen thatconductors material 42. In order to obtain the structure depicted inFIG. 2 , one may simultaneouslycoat conductors conductors - The insulating
material 42 that is disposed betweenconductors 14/16, may be the same as the insulatingmaterial 44/46 that is disposed aboveconductor 14 and belowconductor 16. Alternatively, and as dictated by the choice of processing steps and materials, the insulatingmaterial 42 may be different from the insulatingmaterial 44 and/or the insulatingmaterial 46. Thus, step 48 of the process describes disposing insulating material between thecoated conductors step 40; and it may be done thereafter. The insulatingmaterial 42, the insulatingmaterial 44, and the insulatingmaterial 46 each generally has a resistivity of from about 1×109 to about 1×1013 ohm-centimeters. - After the insulating
material 42/44/46 has been deposited, and in one embodiment, the coated conductor assembly is preferably heat treated instep 50. This heat treatment often is used in conjunction with coating processes in which the heat is required to bond the insulative material to theconductors 14/16. - The heat-treatment step may be conducted after the deposition of the insulating
material 42/44/46, or it may be conducted simultaneously therewith. In either event, and when it is used, it is preferred to heat thecoated conductors 14/16 to a temperature of from about 200 to about 600 degrees Centigrade for from about 1 minute to about 10 minutes. - Referring again to
FIG. 1A , and instep 52 of the process, after thecoated conductors 14/16 have been subjected toheat treatment step 50, they are allowed to cool to a temperature of from about 30 to about 100 degrees Centigrade over a period of time of from about 3 to about 15 minutes. - One need not invariably heat treat and/or cool. Thus, referring to FIG. IA, one may immediately coat nanomagnetic particles onto to the
coated conductors 14/16 instep 54 either afterstep 48 and/or afterstep 50 and/or afterstep 52. - In
step 54, nanomagnetic materials are coated onto the previously coatedconductors FIG. 2 , wherein the nanomagnetic particles are identified asparticles 24. In general, and as is known to those skilled in the art, nanomagnetic material is magnetic material which has an average particle size less than 100 nanometers and, preferably, in the range of from about 2 to 50 nanometers. Reference may be had, e.g., to U.S. Pat. No. 5,889,091 (rotationally free nanomagnetic material), U.S. Pat. Nos. 5,714,536, 5,667,924, and the like. The entire disclosure of each of these United States patents is hereby incorporated by reference into this specification. - The nanomagnetic materials may be, e.g., nano-sized ferrites such as, e.g., the nanomagnetic ferrites disclosed in U.S. Pat. No. 5,213,851, the entire disclosure of which is hereby incorporated by reference into this specification. This patent claims a process for coating a layer of ferritic material with a thickness of from about 0.1 to about 500 microns onto a substrate at a deposition rate of from about 0.01 to about 10 microns per minute per 35 square centimeters of substrate surface, comprising the steps of: (a) providing a solution comprised of a first compound and a second compound, wherein said first compound is an iron compound and said second compound is selected from the group consisting of compounds of nickel, zinc, magnesium, strontium, barium, manganese, lithium, lanthanum, yttrium, scandium, samarium, europium, terbium, dysprosium, holmium, erbium, ytterbium, lutetium, cerium, praseodymium, thulium, neodymium, gadolinium, aluminum, iridium, lead, chromium, gallium, indium, chromium, samarium, cobalt, titanium, and mixtures thereof, and wherein said solution is comprised of from about 0.01 to about 1,000 grams of a mixture consisting essentially of said compounds per liter of said solution; (b) subjecting said solution to ultrasonic sound waves at a frequency in excess of 20,000 hertz, and to an atmospheric pressure of at least about 600 millimeters of mercury, thereby causing said solution to form into an aerosol; (c) providing a radio frequency plasma reactor comprised of a top section, a bottom section, and a radio-frequency coil; (d) generating a hot plasma gas within said radio frequency plasma reactor, thereby producing a plasma region; (e) providing a flame region disposed above said top section of said radio frequency plasma reactor; (f) contacting said aerosol with said hot plasma gas within said plasma reactor while subjecting said aerosol to an atmospheric pressure of at least about 600 millimeters of mercury and to a radio frequency alternating current at a frequency of from about 100 kilohertz to about 30 megahertz, thereby forming a vapor; (g) providing a substrate disposed above said flame region; and (h) contacting said vapor with said substrate, thereby forming said layer of ferritic material.
- By way of further illustration, one may use the techniques described in an article by M. De Marco, X. W. Wang, et al. on “Mossbauer and magnetization studies of nickel ferrites” published in the Journal of Applied Physics 73(10), May 15, 1993, at pages 6287-6289.
- In general, the thickness of the layer of nanomagnetic material deposited onto the
coated conductors 14/16 is less than about 5 microns and generally from about 0.1 to about 3 microns. - After the nanomagnetic material is coated in
step 54, the coated assembly may be optionally heat-treated instep 56. In thisoptional step 56, it is preferred to subject thecoated conductors 14/16 to a temperature of from about 200 to about 600 degrees Centigrade for from about I to about 10 minutes. In one embodiment, illustrated inFIG. 3 , one or more additional insulatinglayers 43 are coated onto the assembly depicted inFIG. 2 , by one or more of the processes disclosed hereinabove. This is conducted in optional step 58 (see FIG. IA). -
FIG. 4 is a partial schematic view of theassembly 11 ofFIG. 2 , illustrating the current flow in such assembly. Referring goFIG. 4 , it will be seen that current flows intoconductor 14 in the direction ofarrow 60, and it flows out ofconductor 16 in the direction ofarrow 62. The net current flow through theassembly 11 is zero; and the net Lorentz force in theassembly 11 is thus zero. Consequently, even high current flows in theassembly 11 do not cause such assembly to move. - In the embodiment depicted in
FIG. 4 ,conductors - In the embodiment depicted in
FIG. 4 , and in one preferred aspect thereof, theconductors - Referring again to
FIG. 4 , thenanomagnetic particles 24 are present in a density sufficient so as to provide shielding from magnetic flux lines 64. Without wishing to be bound to any particular theory, applicant believes that thenanomagnetic particles 24 trap and pin the magnetic lines offlux 64. - In order to function optimally, the
nanomagnetic particles 24 have a specified magnetization. As is known to those skilled in the art, magnetization is the magnetic moment per unit volume of a substance. Reference may be had, e.g., to U.S. Pat. Nos. 4,169,998, 4,168,481, 4,166,263, 5,260,132, 4,778,714, and the like. The entire disclosure of each of these United States patents is hereby incorporated by reference into this specification. - Referring again to
FIG. 4 , the layer ofnanomagnetic particles 24 preferably has a saturation magnetization, at 25 degrees Centigrade, of from about 200 to about 25,000 Gauss, or higher. In one embodiment, the saturation magnetization at room temperature of the nanomagnetic particles is from about 500 to about 10,000 Gauss. For a discussion of the saturation magnetization of various materials, reference may be had, e.g., to U.S. Pat. Nos. 4,705,613, 4,631,613, 5,543,070, 3,901,741 (cobalt, samarium, and gadolinium alloys), and the like. The entire disclosure of each of these United States patents is hereby incorporated by reference into this specification. As will be apparent to those skilled in the art, especially upon studying the aforementioned patents, the saturation magnetization of thin films is often higher than the saturation magnetization of bulk objects. - In one embodiment, it is preferred to utilize a thin film with a thickness of less than about 2 microns and a saturation magnetization in excess of 20,000 Gauss. The thickness of the layer of nanomagnetic material is measured from the bottom surface of the layer that contains such material to the top surface of such layer that contains such material; and such bottom surface and/or such top surface may be contiguous with other layers of material (such as insulating material) that do not contain nanomagnetic particles.
- Thus, e.g., one may make a thin film in accordance with the procedure described at page 156 of Nature, Volume 407, Sep. 14, 2000, that describes a multilayer thin film has a saturation magnetization of 24,000 Gauss. By the appropriate selection of nanomagnetic particles, and the thickness of the films deposited, one may obtain saturation magnetizations of as high as at least about 26,000.
- In the preferred embodiment depicted in
FIG. 4 , thenanomagnetic particles 24 are disposed within an insulating matrix so that any heat produced by such particles will be slowly dispersed within such matrix. Such matrix, as indicated hereinabove, may be made from ceria, calcium oxide, silica, alumina. In general, the insulatingmaterial 42 preferably has a thermal conductivity of less than about 20 (calories centimeters/square centimeters-degree second)×10,000. See, e.g., page E-6 of the 63rd Edition of the “Handbook of Chemistry and Physics” (CRC Press, Inc., Boca Raton, Fla., 1982). - The
nanomagnetic materials 24 typically comprise one or more of iron, cobalt, nickel, gadolinium, and samarium atoms. Thus, e.g., typical nanomagnetic materials include alloys of iron and nickel (permalloy), cobalt, niobium, and zirconium (CNZ), iron, boron, and nitrogen, cobalt, iron, boron, and silica, iron, cobalt, boron, and fluoride, and the like. These and other materials are descried in a book by J. Douglas Adam et al. entitled “Handbook of Thin Film Devices” (Academic Press, San Diego, Calif., 2000). Chapter 5 of this book beginning at page 185, describes “magnetic films for planar inductive components and devices;” and Tables 5.1 and 5.2 in this chapter describe many magnetic materials. -
FIG. 5 is a sectional view of theassembly 11 ofFIG. 2 . The device ofFIG. 5 , and of the other Figures of this application, is preferably substantially flexible. As used in this specification, the term flexible refers to an assembly that can be bent to form a circle with a radius of less than 2 centimeters without breaking. Put another way, the bend radius of thecoated assembly 11 can be less than 2 centimeters. Reference may be had, e.g., to U.S. Pat. Nos. 4,705,353; 5,946,439; 5,315,365; 4,641,917; 5,913,005; and the like. The entire disclosure of each of these United States patents is hereby incorporated by reference into this specification. - As will be apparent, even when the magnetic insulating properties of the assembly of this invention are not 100 percent effective, the assembly still prevents the rapid dissipation of heat to bodily tissue.
-
FIGS. 6A and 6B are side and end sectional views of anotherpreferred conductor assembly 101 of this invention. Theassembly 101 is similar in configuration to theassembly 11 but differs therefrom in that only oneconductor 14 is utilized. Disposed aroundconductor 14 are a layer of insulatingmaterial 44, a layer ofnanoelectrical material 102, and a layer ofnanomagnetic material 100. - The layer of
nanoelectrical material 102 preferably has a thickness of from about 0.5 to about 2 microns. The nanoelectricalmaterial comprising layer 102 has a resistivity of from about 1.6 to about 100 microohm-centimeters. As is known to those skilled in the art, when nanoelectrical material is exposed to electromagnetic radiation, and in particular to an electric field, it will shield the substrate over which it is disposed from such electrical field. Reference may be had, e.g., to International patent publication WO9820719 in which reference is made to U.S. Pat. No. 4,963,291; each of these patents and patent applications is hereby incorporated by reference into this specification. - As is disclosed in U.S. Pat. No. 4,963,291 of Bercaw, one may produce electromagnetic shielding resins comprised of electroconductive particles, such as iron, aluminum, copper, silver and steel in sizes ranging from 0.5 to 0.50 microns. The entire disclosure of this United States patent is hereby incorporated by reference into this specification.
- The nanoelectrical particles used in this invention preferably have a particle size within the range of from about I to about 100 microns, and a resistivity of from about 1.6 to about 100 microohm-centimeters. In one embodiment, such nanoelectrical particles comprise a mixture of iron and aluminum. In another embodiment, such nanoelectrical particles consist essentially of a mixture of iron and aluminum. It is preferred that, in such nanoelectrical particles, and in one embodiment, at least 9 moles of aluminum are present for each mole of iron. In another embodiment, at least about 9.5 moles of aluminum are present for each mole of iron. In yet another embodiment, at least 9.9 moles of aluminum are present for each mole of iron.
-
FIGS. 7A and 7B are end and side sectional views ofconductor assembly 120 that is similar to the assembly 101 (seeFIGS. 6A and 6B ) but differs therefrom in that the nanoelectrical material and the nanomagnetic material are both disposed in thesame layer 105. One may produce such alayer 105 by simultaneously depositing the nanoelectrical particles and the nanomagnetic particles with, e.g., sputtering technology. -
FIG. 8 is schematic representation of acoated conductor assembly 130 comprised offlexible conductor 14 andcoating 105. In the embodiment depicted, thecoating 105 contains both nanomagnetic and nanoelectrical particles. In another embodiment, not shown, thecoating 105 contains only nanomagnetic particles. - Referring to
FIG. 8 , it will be seen thatsections coating 105. Theuncoated sections 134 et seq. are less likely to increase their temperature upon being exposed to electromagnetic radiation and, thus, can more readily be contacted with the tissue of a biological organism. - It is to be understood that the aforementioned description is illustrative only and that changes can be made in the apparatus, in the ingredients and their proportions, and in the sequence of combinations and process steps, as well as in other aspects of the invention discussed herein, without departing from the scope of the invention as defined in the following claims.
- Thus, e.g., although one embodiment of the process of this invention has been illustrated with regard to two separate,
non-contiguous conductors
Claims (44)
1. A magnetically shielded conductor assembly comprised of a
a. conductor wherein said conductor has a resistivity of from about 1 to about 100 microohm-centimeters;
b. an insulation shield disposed around said conductor wherein said insulation shield is comprised of an insulating material and electrically insulating particles wherein
1. at least about 90 weight percent of said electrically insulating particles have a maximum dimension of less than about 100 nanometers;
2. said insulation shield has a saturation magnetization at 25 degrees Centigrade of at least about 2,000 Gauss; and
3. said insulation shield has a resistivity of from about 1×109 to about 1×1013 ohm-centimeter.
2. The magnetically shielded conductor assembly as recited in claim 1 , wherein said insulation shield has a saturation magnetization at 25 degrees Centigrade of at least about 10,000 Gauss.
3. The magnetically shielded conductor assembly as recited in claim 2 , wherein said insulation shield has a saturation magnetization at 25 degrees Centigrade of at least about 26,000 Gauss.
4. The magnetically shielded conductor assembly as recited in claim 1 , further comprising an electrical shield which is comprised of electrically conductive particles wherein
a. at least about 90 weight percent of said electrically conductive particles have a maximum dimension of less than about 100 microns;
b. said electrical shield has a resistivity of from about 1.6 to about 100 microohm-centimeters; and
c. said electrical shield is not contiguous with said conductor.
5. The magnetically shielded conductor assembly as recited in claim 4 , further comprising a power source.
6. The magnetically shielded conductor assembly as recited in claim 5 , further comprising a load and a controller wherein said power source is operatively connected to said controller and said controller is operatively connected to said load.
7. The magnetically shielded conductor assembly as recited in claim 6 , wherein said controller is disposed within said insulation shield.
8. The magnetically shielded conductor assembly as recited in claim 7 , wherein said power source supplies alternating current.
9. The magnetically shielded conductor assembly as recited in claim 7 , wherein said power source supplies direct current.
10. The magnetically shielded conductor assembly as recited in claim 7 , wherein said magnetically shielded conductor assembly is operatively configured to be implanted within a biological organism.
11. The magnetically shielded conductor assembly as recited in claim 10 , wherein said load is selected from the group consisting of a pacemaker, an artificial heart, a heart-massaging device, and a defibrillator.
12. The magnetically shielded conductor assembly as recited in claim 4 , wherein said insulating material is selected from the group consisting of silicon dioxide, aluminum oxide, cerium oxide, yttrium-stabilized zirconia, silica carbide, silicon nitride, aluminum nitride, and combinations thereof.
13. The magnetically shielded conductor assembly as recited in claim 4 , wherein said at least about 90 weight percent of said electrically insulating particles and said electrically conductive particles have a maximum dimension of from about 2 to about 50 nanometers.
14. The magnetically shielded conductor assembly as recited in claim 4 , wherein said conductor consists essentially of a conductive material selected from the group consisting of silver, copper, aluminum, alloys thereof, and mixtures thereof.
15. The magnetically shielded conductor assembly as recited in claim 4 , further comprising a second conductor wherein said second conductor has a resistivity of from about 1 to about 100 microohm-centimeters and wherein said insulation shield disposed around said second conductor.
16. The magnetically shielded conductor assembly as recited in claim 15 , wherein said conductor and said second conductor are substantially parallel to each other.
17. The magnetically shielded conductor assembly as recited in claim 15 , further comprising an insulating matrix wherein said insulating matrix is disposed between said conductor and said second conductor.
18. The magnetically shielded conductor assembly as recited in claim 17 , wherein said insulating matrix has a resistivity of from about 1×109 to about 1×1013 ohm-centimeters.
19. The magnetically shielded conductor assembly as recited in claim 18 , wherein said insulating matrix consists essentially of said insulating material.
20. The magnetically shielded conductor assembly as recited in claim 4 , wherein said electrically insulating particles are comprised of ferrites.
21. The magnetically shielded conductor assembly as recited in claim 4 , wherein said insulation shield is a layer with a thickness of less than about 5 microns.
22. The magnetically shielded conductor assembly as recited in claim 21 , wherein said insulation shield is a layer with a thickness of from about 0.1 microns to about 3 microns.
23. The magnetically shielded conductor assembly as recited in claim 22 , wherein said electrical shield is a layer with a thickness of from about 0.1 microns to about 3 microns.
24. The magnetically shielded conductor assembly as recited in claim 4 , wherein said insulating material has a thermal conductivity of less than about 200,000 calories centimeters per square centimeter degree seconds.
25. The magnetically shielded conductor assembly as recited in claim 24 , wherein said magnetically shielded conductor assembly is flexible, having a bend radius of less than 2 centimeters.
26. A magnetically shielded conductor assembly comprised of a
a. a first conductor;
b. a second conductor wherein said first conductor and said second conductor are substantially parallel to one another;
c. an insulation shield disposed around said first conductor and said second doctor wherein said insulation shield is comprised electrically insulating particles wherein
1. at least about 90 weight percent of said electrically insulating particles have a maximum dimension of less than about 100 nanometers;
2. said insulation shield has a saturation magnetization at 25 degrees Centigrade of at least about 2,000 Gauss.
27. The magnetically shielded conductor assembly as recited in claim 23 , wherein said insulation shield is further comprised of an insulating material.
28. The magnetically shielded conductor assembly as recited in claim 27 , wherein said insulation shield has a saturation magnetization at 25 degrees Centigrade of at least about 10,000 Gauss.
29. The magnetically shielded conductor assembly as recited in claim 28 , wherein said insulation shield has a saturation magnetization at 25 degrees Centigrade of at least about 26,000 Gauss.
30. The magnetically shielded conductor assembly as recited in claim 29 , wherein said electrically conductive particles are selected from the group consisting of iron, aluminum, copper silver and steel.
31. The magnetically shielded conductor assembly as recited in claim 30 , wherein at least about 90 weight percent of said electrically conductive particles have a maximum dimension of less than about 100 nanometers.
32. The magnetically shielded conductor assembly as recited in claim 31 , wherein said electrically conductive particles are comprised of iron and aluminum.
33. The magnetically shielded conductor assembly as recited in claim 32 , wherein said electrically conductive particles consist essentially of iron and aluminum.
34. The magnetically shielded conductor assembly as recited in claim 33 , wherein the molar ratio of aluminum to iron at least about 9 to 1.
35. The magnetically shielded conductor assembly as recited in claim 33 , wherein the molar ratio of aluminum to iron at least about 9.5 to 1.
36. The magnetically shielded conductor assembly as recited in claim 33 , wherein the molar ratio of aluminum to iron at least about 9.9 to 1.
37. The magnetically shielded conductor assembly as recited in claim 36 , wherein said electrically conducting particles and said electrically insulating particles are present in the same layer.
38. The magnetically shielded conductor assembly as recited in claim 36 , wherein said electrically conducting particles and said electrically insulating particles are present in two separate layers.
39. The magnetically shielded conductor assembly as recited in claim 36 , wherein said first conductor and said second conductor are contiguous with one another.
40. The magnetically shielded conductor assembly as recited in claim 36 , wherein said first conductor and said second conductor are non-contiguous with one another.
41. A process for producing a magnetically shielded conductor assembly comprising the steps of
a. coating a first conductor and a second conductor with an insulating material thus forming a coated conductor assembly, wherein
i. said insulating material has a resistivity of from about 1×109 to about 1×1013 ohm-centimeter;
ii. said first conductor and said second conductor each have a resistivity of from about 1 to about 100 microohm-centimeters;
b. dispose an insulating matrix between said first conductor and second conductor of said coated conductor assembly to form an insulated conductor assembly, wherein said insulating matrix has a resistivity of from about 1×109 to about 1×1013 ohm-centimeter; and
c. coating said insulated conductor assembly with an insulation shield such that said insulation shield is disposed around said conductor wherein said insulation shield is comprised of said insulating material and electrically insulating particles, thus forming an electrically insulated conductor assembly, wherein
1. at least about 90 weight percent of said electrically insulating particles have a maximum dimension of less than about 100 nanometers;
2. said insulation shield has a saturation magnetization at 25 degrees Centigrade of at least about 2,000 Gauss;
3. said insulation shield has a resistivity of from about 1×109 to about 1×1013 ohm-centimeter;
42. The process for producing a magnetically shielded conductor assembly as recited in claim 41 , further comprising the step of heating said insulated conductor assembly to a temperature of from about 200 degrees to about 600 degrees Centigrade for from about 1 minute to about 10 minutes so as to bond said insulating material to said first conductor and said second conductor.
43. The process for producing a magnetically shielded conductor assembly as recited in claim 42 , further comprising the step of cooling said insulated conductor assembly to a temperature of from about 30 degrees to about 100 degrees Centigrade over a period of from about 3 minutes to about 15 minutes.
44. The process for producing a magnetically shielded conductor assembly as recited in claim 43 , further comprising the step of heating said electrically insulated conductor assembly to a temperature of from about 200 degrees to about 600 degrees Centigrade for from about 1 to about 10 minutes so as to bond said electrically insulating particles to said magnetically shielded conductor assembly.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US11/085,415 US20050182471A1 (en) | 2002-01-22 | 2005-03-21 | Magnetically shielded conductor |
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10/054,407 US6506972B1 (en) | 2002-01-22 | 2002-01-22 | Magnetically shielded conductor |
US10/229,183 US6876886B1 (en) | 2002-01-22 | 2002-08-26 | Magnetically shielded conductor |
US11/085,415 US20050182471A1 (en) | 2002-01-22 | 2005-03-21 | Magnetically shielded conductor |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/229,183 Continuation US6876886B1 (en) | 2002-01-22 | 2002-08-26 | Magnetically shielded conductor |
Publications (1)
Publication Number | Publication Date |
---|---|
US20050182471A1 true US20050182471A1 (en) | 2005-08-18 |
Family
ID=21990858
Family Applications (5)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/054,407 Expired - Fee Related US6506972B1 (en) | 2002-01-09 | 2002-01-22 | Magnetically shielded conductor |
US10/090,553 Expired - Fee Related US6930242B1 (en) | 2002-01-22 | 2002-03-04 | Magnetically shielded conductor |
US10/229,183 Expired - Fee Related US6876886B1 (en) | 2002-01-22 | 2002-08-26 | Magnetically shielded conductor |
US10/260,247 Expired - Fee Related US6673999B1 (en) | 2002-01-22 | 2002-09-30 | Magnetically shielded assembly |
US11/085,415 Abandoned US20050182471A1 (en) | 2002-01-22 | 2005-03-21 | Magnetically shielded conductor |
Family Applications Before (4)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/054,407 Expired - Fee Related US6506972B1 (en) | 2002-01-09 | 2002-01-22 | Magnetically shielded conductor |
US10/090,553 Expired - Fee Related US6930242B1 (en) | 2002-01-22 | 2002-03-04 | Magnetically shielded conductor |
US10/229,183 Expired - Fee Related US6876886B1 (en) | 2002-01-22 | 2002-08-26 | Magnetically shielded conductor |
US10/260,247 Expired - Fee Related US6673999B1 (en) | 2002-01-22 | 2002-09-30 | Magnetically shielded assembly |
Country Status (1)
Country | Link |
---|---|
US (5) | US6506972B1 (en) |
Cited By (34)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20050222657A1 (en) * | 2004-03-30 | 2005-10-06 | Wahlstrand Carl D | MRI-safe implantable lead |
US20090149933A1 (en) * | 2007-12-06 | 2009-06-11 | Cardiac Pacemakers, Inc. | Implantable lead having a variable coil conductor pitch |
US20100234929A1 (en) * | 2009-03-12 | 2010-09-16 | Torsten Scheuermann | Thin profile conductor assembly for medical device leads |
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 |
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 |
US8666512B2 (en) | 2011-11-04 | 2014-03-04 | Cardiac Pacemakers, Inc. | Implantable medical device lead including inner coil reverse-wound relative to shocking coil |
US8666508B2 (en) | 2008-02-06 | 2014-03-04 | Cardiac Pacemakers, Inc. | Lead with MRI compatible design features |
US8670840B2 (en) | 2006-11-30 | 2014-03-11 | Cardiac Pacemakers, Inc. | RF rejecting lead |
US8676351B2 (en) | 2009-12-31 | 2014-03-18 | Cardiac Pacemakers, Inc. | MRI conditionally safe lead with low-profile multi-layer conductor for longitudinal expansion |
US8688236B2 (en) | 2008-05-09 | 2014-04-01 | Cardiac Pacemakers, Inc. | Medical lead coil conductor with spacer element |
US8744600B2 (en) | 2009-06-26 | 2014-06-03 | Cardiac Pacemakers, Inc. | Medical device lead including a unifilar coil with improved torque transmission capacity and reduced MRI heating |
US8798767B2 (en) | 2009-12-31 | 2014-08-05 | Cardiac Pacemakers, Inc. | MRI conditionally safe lead with multi-layer conductor |
US8825179B2 (en) | 2012-04-20 | 2014-09-02 | Cardiac Pacemakers, Inc. | Implantable medical device lead including a unifilar coiled cable |
US8825181B2 (en) | 2010-08-30 | 2014-09-02 | Cardiac Pacemakers, Inc. | Lead conductor with pitch and torque control for MRI conditionally safe use |
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 |
US8983623B2 (en) | 2012-10-18 | 2015-03-17 | Cardiac Pacemakers, Inc. | Inductive element for providing MRI compatibility in an implantable medical device lead |
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 |
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 |
US9254380B2 (en) | 2009-10-19 | 2016-02-09 | Cardiac Pacemakers, Inc. | MRI compatible tachycardia lead |
US9463317B2 (en) | 2012-04-19 | 2016-10-11 | Medtronic, Inc. | Paired medical lead bodies with braided conductive shields having different physical parameter values |
US9504821B2 (en) | 2014-02-26 | 2016-11-29 | Cardiac Pacemakers, Inc. | Construction of an MRI-safe tachycardia lead |
US9731119B2 (en) | 2008-03-12 | 2017-08-15 | Medtronic, Inc. | System and method for implantable medical device lead shielding |
US9750944B2 (en) | 2009-12-30 | 2017-09-05 | Cardiac Pacemakers, Inc. | MRI-conditionally safe medical device lead |
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 |
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 |
US10537730B2 (en) | 2007-02-14 | 2020-01-21 | Medtronic, Inc. | Continuous conductive materials for electromagnetic shielding |
Families Citing this family (205)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US7713297B2 (en) * | 1998-04-11 | 2010-05-11 | Boston Scientific Scimed, Inc. | Drug-releasing stent with ceramic-containing layer |
US8244370B2 (en) * | 2001-04-13 | 2012-08-14 | Greatbatch Ltd. | Band stop filter employing a capacitor and an inductor tank circuit to enhance MRI compatibility of active medical devices |
US20080229590A1 (en) * | 2001-01-22 | 2008-09-25 | Robert Garrett | Roofmates shingle knife |
US20070168006A1 (en) * | 2001-02-20 | 2007-07-19 | Biophan Technologies, Inc. | Medical device with an electrically conductive anti-antenna member |
US20070168005A1 (en) * | 2001-02-20 | 2007-07-19 | Biophan Technologies, Inc. | Medical device with an electrically conductive anti-antenna member |
US20050288750A1 (en) * | 2003-08-25 | 2005-12-29 | Biophan Technologies, Inc. | Medical device with an electrically conductive anti-antenna member |
US6829509B1 (en) * | 2001-02-20 | 2004-12-07 | Biophan Technologies, Inc. | Electromagnetic interference immune tissue invasive system |
US20050288753A1 (en) * | 2003-08-25 | 2005-12-29 | Biophan Technologies, Inc. | Medical device with an electrically conductive anti-antenna member |
US20050283167A1 (en) * | 2003-08-25 | 2005-12-22 | Biophan Technologies, Inc. | Medical device with an electrically conductive anti-antenna member |
US20050283214A1 (en) * | 2003-08-25 | 2005-12-22 | Biophan Technologies, Inc. | Medical device with an electrically conductive anti-antenna member |
US6949929B2 (en) * | 2003-06-24 | 2005-09-27 | Biophan Technologies, Inc. | Magnetic resonance imaging interference immune device |
US20070173911A1 (en) * | 2001-02-20 | 2007-07-26 | Biophan Technologies, Inc. | Medical device with an electrically conductive anti-antenna member |
CA2482202C (en) | 2001-04-13 | 2012-07-03 | Surgi-Vision, Inc. | Systems and methods for magnetic-resonance-guided interventional procedures |
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 |
US7727221B2 (en) | 2001-06-27 | 2010-06-01 | Cardiac Pacemakers Inc. | Method and device for electrochemical formation of therapeutic species in vivo |
US7011647B2 (en) * | 2001-07-13 | 2006-03-14 | Scimed Life Systems, Inc. | Introducer sheath |
US7150737B2 (en) * | 2001-07-13 | 2006-12-19 | Sci/Med Life Systems, Inc. | Methods and apparatuses for navigating the subarachnoid space |
JP3833926B2 (en) * | 2001-11-05 | 2006-10-18 | 日本電子株式会社 | Linear member and method of manufacturing linear member |
US6506972B1 (en) * | 2002-01-22 | 2003-01-14 | Nanoset, Llc | Magnetically shielded conductor |
US6768053B1 (en) * | 2002-01-09 | 2004-07-27 | Nanoset, Llc | Optical fiber assembly |
US6906256B1 (en) * | 2002-01-22 | 2005-06-14 | Nanoset, Llc | Nanomagnetic shielding assembly |
US20040225213A1 (en) * | 2002-01-22 | 2004-11-11 | Xingwu Wang | Magnetic resonance imaging coated assembly |
WO2003061755A2 (en) * | 2002-01-22 | 2003-07-31 | Nanoset, Llc | Nanomagnetically shielded substrate |
US7091412B2 (en) * | 2002-03-04 | 2006-08-15 | Nanoset, Llc | Magnetically shielded assembly |
US20050178584A1 (en) * | 2002-01-22 | 2005-08-18 | Xingwu Wang | Coated stent and MR imaging thereof |
US7162302B2 (en) * | 2002-03-04 | 2007-01-09 | Nanoset Llc | Magnetically shielded assembly |
US20050260331A1 (en) * | 2002-01-22 | 2005-11-24 | Xingwu Wang | Process for coating a substrate |
US20050247472A1 (en) * | 2002-01-22 | 2005-11-10 | Helfer Jeffrey L | Magnetically shielded conductor |
US6844492B1 (en) * | 2002-01-22 | 2005-01-18 | Nanoset, Llc | Magnetically shielded conductor |
US20040210289A1 (en) * | 2002-03-04 | 2004-10-21 | Xingwu Wang | Novel nanomagnetic particles |
US7127294B1 (en) * | 2002-12-18 | 2006-10-24 | Nanoset Llc | Magnetically shielded assembly |
US8396568B2 (en) * | 2002-04-11 | 2013-03-12 | Medtronic, Inc. | Medical electrical lead body designs incorporating energy dissipating shunt |
JP4614281B2 (en) * | 2002-12-16 | 2011-01-19 | ジーイー・ヘルスケア・アクスイェ・セルスカプ | Magnetic resonance imaging method and compound used in the method |
US20040199069A1 (en) * | 2003-04-02 | 2004-10-07 | Connelly Patrick R. | Device and method for preventing magnetic resonance imaging induced damage |
US20050240100A1 (en) * | 2003-04-08 | 2005-10-27 | Xingwu Wang | MRI imageable medical device |
US20050155779A1 (en) * | 2003-04-08 | 2005-07-21 | Xingwu Wang | Coated substrate assembly |
US20070010702A1 (en) * | 2003-04-08 | 2007-01-11 | Xingwu Wang | Medical device with low magnetic susceptibility |
US20050261763A1 (en) * | 2003-04-08 | 2005-11-24 | Xingwu Wang | Medical device |
US20050149002A1 (en) * | 2003-04-08 | 2005-07-07 | Xingwu Wang | Markers for visualizing interventional medical devices |
US20050119725A1 (en) * | 2003-04-08 | 2005-06-02 | Xingwu Wang | Energetically controlled delivery of biologically active material from an implanted medical device |
US20040254419A1 (en) * | 2003-04-08 | 2004-12-16 | Xingwu Wang | Therapeutic assembly |
US20060102871A1 (en) * | 2003-04-08 | 2006-05-18 | Xingwu Wang | Novel composition |
US20050244337A1 (en) * | 2003-04-08 | 2005-11-03 | Xingwu Wang | Medical device with a marker |
US20050278020A1 (en) * | 2003-04-08 | 2005-12-15 | Xingwu Wang | Medical device |
US20050079132A1 (en) * | 2003-04-08 | 2005-04-14 | Xingwu Wang | Medical device with low magnetic susceptibility |
US20050025797A1 (en) * | 2003-04-08 | 2005-02-03 | Xingwu Wang | Medical device with low magnetic susceptibility |
US20050149169A1 (en) * | 2003-04-08 | 2005-07-07 | Xingwu Wang | Implantable medical device |
US7839146B2 (en) * | 2003-06-24 | 2010-11-23 | Medtronic, Inc. | Magnetic resonance imaging interference immune device |
US7388378B2 (en) * | 2003-06-24 | 2008-06-17 | Medtronic, Inc. | Magnetic resonance imaging interference immune device |
US20050050042A1 (en) * | 2003-08-20 | 2005-03-03 | Marvin Elder | Natural language database querying |
US20050288754A1 (en) * | 2003-08-25 | 2005-12-29 | Biophan Technologies, Inc. | Medical device with an electrically conductive anti-antenna member |
US20050288756A1 (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 |
US20050288755A1 (en) * | 2003-08-25 | 2005-12-29 | 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 |
US20050288752A1 (en) * | 2003-08-25 | 2005-12-29 | Biophan Technologies, 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 |
US7344559B2 (en) * | 2003-08-25 | 2008-03-18 | Biophan Technologies, Inc. | Electromagnetic radiation transparent device and method of making thereof |
US20050065587A1 (en) * | 2003-09-24 | 2005-03-24 | Mark Gryzwa | Implantable lead with magnetic jacket |
US20050070972A1 (en) * | 2003-09-26 | 2005-03-31 | Wahlstrand Carl D. | Energy shunt for producing an MRI-safe implantable medical device |
EP1522266A1 (en) * | 2003-10-06 | 2005-04-13 | Stryker Trauma SA | External fixation elements |
JP2005128771A (en) * | 2003-10-23 | 2005-05-19 | Fujitsu Ltd | Data file system, data access server, and data access program |
US20070027532A1 (en) * | 2003-12-22 | 2007-02-01 | Xingwu Wang | Medical device |
US7765005B2 (en) * | 2004-02-12 | 2010-07-27 | Greatbatch Ltd. | Apparatus and process for reducing the susceptability of active implantable medical devices to medical procedures such as magnetic resonance imaging |
US7174219B2 (en) * | 2004-03-30 | 2007-02-06 | Medtronic, Inc. | Lead electrode for use in an MRI-safe implantable medical device |
US7491263B2 (en) * | 2004-04-05 | 2009-02-17 | Technology Innovation, Llc | Storage assembly |
US7758892B1 (en) * | 2004-05-20 | 2010-07-20 | Boston Scientific Scimed, Inc. | Medical devices having multiple layers |
FR2873324B1 (en) * | 2004-07-22 | 2006-10-27 | Bic Sa Soc | LIQUID SUPPLY UNIT FOR A LIQUID PROJECTION INSTRUMENT AND A LIQUID PROJECTION INSTRUMENT COMPRISING SUCH A LIQUID SUPPLY |
WO2006023700A2 (en) * | 2004-08-20 | 2006-03-02 | Biophan Technologies, Inc. | Magnetic resonance imaging interference immune device |
US20060118758A1 (en) * | 2004-09-15 | 2006-06-08 | Xingwu Wang | Material to enable magnetic resonance imaging of implantable medical devices |
DE102005045071A1 (en) * | 2005-09-21 | 2007-04-12 | Siemens Ag | Catheter device with a position sensor system for the treatment of a partial and / or complete vascular occlusion under image monitoring |
US20060127443A1 (en) * | 2004-12-09 | 2006-06-15 | Helmus Michael N | Medical devices having vapor deposited nanoporous coatings for controlled therapeutic agent delivery |
US8014867B2 (en) * | 2004-12-17 | 2011-09-06 | Cardiac Pacemakers, Inc. | MRI operation modes for implantable medical devices |
US7493167B2 (en) * | 2005-03-22 | 2009-02-17 | Greatbatch-Sierra, Inc. | Magnetically shielded AIMD housing with window for magnetically actuated switch |
US20070100231A1 (en) * | 2005-05-19 | 2007-05-03 | Biophan Technologies, Inc. | Electromagnetic resonant circuit sleeve for implantable medical device |
US7551967B1 (en) | 2005-05-19 | 2009-06-23 | Pacesetter, Inc. | Implantable medical leads and devices having carbon nanotube-based anti-electrostatic coatings and methods for making such leads and devices |
WO2006133365A2 (en) * | 2005-06-08 | 2006-12-14 | Nanoset, Llc | Medical device |
DE102005029270B4 (en) * | 2005-06-23 | 2009-07-30 | Siemens Ag | Catheter, catheter device and diagnostic imaging device |
US20070038176A1 (en) * | 2005-07-05 | 2007-02-15 | Jan Weber | Medical devices with machined layers for controlled communications with underlying regions |
DE102005032755B4 (en) * | 2005-07-13 | 2014-09-04 | Siemens Aktiengesellschaft | System for performing and monitoring minimally invasive procedures |
DE102005045362B4 (en) * | 2005-09-22 | 2012-03-22 | Siemens Ag | Device for determining the position of a medical instrument, associated imaging examination device and associated method |
DE102005045373A1 (en) * | 2005-09-22 | 2007-04-05 | Siemens Ag | catheter device |
DE102005050344A1 (en) | 2005-10-20 | 2007-05-03 | Siemens Ag | Cryocatheter for medical investigation and treatment equipment for e.g. diagnosis and treatment of heart infarcts, has image capture device that maps region of vessel around balloon arranged near catheter tip |
US7917213B2 (en) * | 2005-11-04 | 2011-03-29 | Kenergy, Inc. | MRI compatible implanted electronic medical lead |
DE102005059262B4 (en) * | 2005-12-12 | 2008-02-07 | Siemens Ag | catheter device |
US8840660B2 (en) * | 2006-01-05 | 2014-09-23 | Boston Scientific Scimed, Inc. | Bioerodible endoprostheses and methods of making the same |
US8089029B2 (en) | 2006-02-01 | 2012-01-03 | Boston Scientific Scimed, Inc. | Bioabsorbable metal medical device and method of manufacture |
CA2643280C (en) * | 2006-02-24 | 2014-05-27 | American Bank Note Holographics, Inc. | Method of reducing electro-static discharge (esd) from conductors on insulators |
US20070239256A1 (en) * | 2006-03-22 | 2007-10-11 | Jan Weber | Medical devices having electrical circuits with multilayer regions |
US20070224244A1 (en) * | 2006-03-22 | 2007-09-27 | Jan Weber | Corrosion resistant coatings for biodegradable metallic implants |
US20070224235A1 (en) * | 2006-03-24 | 2007-09-27 | Barron Tenney | Medical devices having nanoporous coatings for controlled therapeutic agent delivery |
US8187620B2 (en) * | 2006-03-27 | 2012-05-29 | Boston Scientific Scimed, Inc. | Medical devices comprising a porous metal oxide or metal material and a polymer coating for delivering therapeutic agents |
DE102006015013B4 (en) * | 2006-03-31 | 2010-06-02 | Siemens Ag | Implantable pacemaker |
US8048150B2 (en) * | 2006-04-12 | 2011-11-01 | Boston Scientific Scimed, Inc. | Endoprosthesis having a fiber meshwork disposed thereon |
US20070264303A1 (en) * | 2006-05-12 | 2007-11-15 | Liliana Atanasoska | Coating for medical devices comprising an inorganic or ceramic oxide and a therapeutic agent |
US8815275B2 (en) | 2006-06-28 | 2014-08-26 | Boston Scientific Scimed, Inc. | Coatings for medical devices comprising a therapeutic agent and a metallic material |
JP2009542359A (en) * | 2006-06-29 | 2009-12-03 | ボストン サイエンティフィック リミテッド | Medical device with selective covering |
CA2658103A1 (en) * | 2006-07-18 | 2008-01-24 | American Bank Note Holographics, Inc. | Holographic magnetic stripe demetalization security |
US8049489B2 (en) * | 2006-07-26 | 2011-11-01 | Cardiac Pacemakers, Inc. | Systems and methods for sensing external magnetic fields in implantable medical devices |
US8052743B2 (en) | 2006-08-02 | 2011-11-08 | Boston Scientific Scimed, Inc. | Endoprosthesis with three-dimensional disintegration control |
DE102006040936A1 (en) * | 2006-08-31 | 2008-03-13 | Siemens Ag | Catheter for removing tissue from a hollow organ |
EP2068757B1 (en) | 2006-09-14 | 2011-05-11 | Boston Scientific Limited | Medical devices with drug-eluting coating |
EP2081616B1 (en) * | 2006-09-15 | 2017-11-01 | Boston Scientific Scimed, Inc. | Bioerodible endoprostheses and methods of making the same |
EP2068782B1 (en) | 2006-09-15 | 2011-07-27 | Boston Scientific Limited | Bioerodible endoprostheses |
JP2010503491A (en) | 2006-09-15 | 2010-02-04 | ボストン サイエンティフィック リミテッド | Bioerodible endoprosthesis with biologically stable inorganic layers |
CA2663220A1 (en) * | 2006-09-15 | 2008-03-20 | Boston Scientific Limited | Medical devices and methods of making the same |
WO2008036457A2 (en) * | 2006-09-18 | 2008-03-27 | Boston Scientific Limited | Controlling biodegradation of a medical instrument |
US8002821B2 (en) * | 2006-09-18 | 2011-08-23 | Boston Scientific Scimed, Inc. | Bioerodible metallic ENDOPROSTHESES |
WO2008045184A1 (en) * | 2006-10-05 | 2008-04-17 | Boston Scientific Limited | Polymer-free coatings for medical devices formed by plasma electrolytic deposition |
US7981150B2 (en) | 2006-11-09 | 2011-07-19 | Boston Scientific Scimed, Inc. | Endoprosthesis with coatings |
US8768486B2 (en) * | 2006-12-11 | 2014-07-01 | Medtronic, Inc. | Medical leads with frequency independent magnetic resonance imaging protection |
US8502684B2 (en) | 2006-12-22 | 2013-08-06 | Geoffrey J. Bunza | Sensors and systems for detecting environmental conditions or changes |
US7812731B2 (en) * | 2006-12-22 | 2010-10-12 | Vigilan, Incorporated | Sensors and systems for detecting environmental conditions or changes |
DE102006061178A1 (en) * | 2006-12-22 | 2008-06-26 | Siemens Ag | Medical system for carrying out and monitoring a minimal invasive intrusion, especially for treating electro-physiological diseases, has X-ray equipment and a control/evaluation unit |
DE602007010669D1 (en) | 2006-12-28 | 2010-12-30 | Boston Scient Ltd | HREN FOR THIS |
US8070797B2 (en) | 2007-03-01 | 2011-12-06 | Boston Scientific Scimed, Inc. | Medical device with a porous surface for delivery of a therapeutic agent |
US8431149B2 (en) | 2007-03-01 | 2013-04-30 | Boston Scientific Scimed, Inc. | Coated medical devices for abluminal drug delivery |
US8067054B2 (en) | 2007-04-05 | 2011-11-29 | Boston Scientific Scimed, Inc. | Stents with ceramic drug reservoir layer and methods of making and using the same |
US7976915B2 (en) * | 2007-05-23 | 2011-07-12 | Boston Scientific Scimed, Inc. | Endoprosthesis with select ceramic morphology |
US8002823B2 (en) * | 2007-07-11 | 2011-08-23 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US7942926B2 (en) | 2007-07-11 | 2011-05-17 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
JP2010533563A (en) | 2007-07-19 | 2010-10-28 | ボストン サイエンティフィック リミテッド | Endoprosthesis with adsorption inhibiting surface |
US7931683B2 (en) | 2007-07-27 | 2011-04-26 | Boston Scientific Scimed, Inc. | Articles having ceramic coated surfaces |
US8815273B2 (en) * | 2007-07-27 | 2014-08-26 | Boston Scientific Scimed, Inc. | Drug eluting medical devices having porous layers |
US8221822B2 (en) * | 2007-07-31 | 2012-07-17 | Boston Scientific Scimed, Inc. | Medical device coating by laser cladding |
JP2010535541A (en) * | 2007-08-03 | 2010-11-25 | ボストン サイエンティフィック リミテッド | Coating for medical devices with large surface area |
US8052745B2 (en) * | 2007-09-13 | 2011-11-08 | Boston Scientific Scimed, Inc. | Endoprosthesis |
US8029554B2 (en) * | 2007-11-02 | 2011-10-04 | Boston Scientific Scimed, Inc. | Stent with embedded material |
US7938855B2 (en) | 2007-11-02 | 2011-05-10 | Boston Scientific Scimed, Inc. | Deformable underlayer for stent |
US20090118813A1 (en) * | 2007-11-02 | 2009-05-07 | Torsten Scheuermann | Nano-patterned implant surfaces |
US8216632B2 (en) | 2007-11-02 | 2012-07-10 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US20090118809A1 (en) * | 2007-11-02 | 2009-05-07 | Torsten Scheuermann | Endoprosthesis with porous reservoir and non-polymer diffusion layer |
US20090143855A1 (en) * | 2007-11-29 | 2009-06-04 | Boston Scientific Scimed, Inc. | Medical Device Including Drug-Loaded Fibers |
US8032228B2 (en) | 2007-12-06 | 2011-10-04 | Cardiac Pacemakers, Inc. | Method and apparatus for disconnecting the tip electrode during MRI |
US8086321B2 (en) | 2007-12-06 | 2011-12-27 | Cardiac Pacemakers, Inc. | Selectively connecting the tip electrode during therapy for MRI shielding |
US8275464B2 (en) | 2007-12-06 | 2012-09-25 | Cardiac Pacemakers, Inc. | Leads with high surface resistance |
EP2224995B1 (en) * | 2007-12-06 | 2015-11-25 | Cardiac Pacemakers, Inc. | Implantable lead with shielding |
US9233240B2 (en) | 2007-12-12 | 2016-01-12 | Pacesetter, Inc. | Systems and methods for determining inductance and capacitance values for use with LC filters within implantable medical device leads to reduce lead heating during MRI |
US20100008970A1 (en) * | 2007-12-14 | 2010-01-14 | Boston Scientific Scimed, Inc. | Drug-Eluting Endoprosthesis |
US8311637B2 (en) | 2008-02-11 | 2012-11-13 | Cardiac Pacemakers, Inc. | Magnetic core flux canceling of ferrites in MRI |
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 |
US9108066B2 (en) | 2008-03-20 | 2015-08-18 | Greatbatch Ltd. | Low impedance oxide resistant grounded capacitor for an AIMD |
US10080889B2 (en) | 2009-03-19 | 2018-09-25 | Greatbatch Ltd. | Low inductance and low resistance hermetically sealed filtered feedthrough for an AIMD |
US8920491B2 (en) | 2008-04-22 | 2014-12-30 | Boston Scientific Scimed, Inc. | Medical devices having a coating of inorganic material |
US8932346B2 (en) | 2008-04-24 | 2015-01-13 | Boston Scientific Scimed, Inc. | Medical devices having inorganic particle layers |
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 |
US7998192B2 (en) * | 2008-05-09 | 2011-08-16 | Boston Scientific Scimed, Inc. | Endoprostheses |
US9025598B1 (en) | 2012-03-22 | 2015-05-05 | Nuax, Inc. | Cable/guidewire/interconnects communication apparatus and methods |
US9242100B2 (en) | 2012-08-07 | 2016-01-26 | Nuax, Inc. | Optical fiber-fine wire lead for electrostimulation and sensing |
US9193313B2 (en) | 2012-03-22 | 2015-11-24 | Nuax, Inc. | Methods and apparatuses involving flexible cable/guidewire/interconnects |
US8692117B2 (en) | 2008-05-28 | 2014-04-08 | Cardia Access, Inc. | Durable fine wire electrical conductor suitable for extreme environment applications |
US9513443B2 (en) | 2008-05-28 | 2016-12-06 | John Lawrence Erb | Optical fiber-fine wire conductor and connectors |
US8236046B2 (en) | 2008-06-10 | 2012-08-07 | Boston Scientific Scimed, Inc. | Bioerodible endoprosthesis |
US8449603B2 (en) | 2008-06-18 | 2013-05-28 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US20100004733A1 (en) * | 2008-07-02 | 2010-01-07 | Boston Scientific Scimed, Inc. | Implants Including Fractal Structures |
US7985252B2 (en) * | 2008-07-30 | 2011-07-26 | Boston Scientific Scimed, Inc. | Bioerodible endoprosthesis |
US20100036466A1 (en) * | 2008-08-11 | 2010-02-11 | Pacesetter, Inc. | Lead construction with composite material shield layer |
US8571661B2 (en) * | 2008-10-02 | 2013-10-29 | Cardiac Pacemakers, Inc. | Implantable medical device responsive to MRI induced capture threshold changes |
US8382824B2 (en) * | 2008-10-03 | 2013-02-26 | Boston Scientific Scimed, Inc. | Medical implant having NANO-crystal grains with barrier layers of metal nitrides or fluorides |
US20110015713A1 (en) * | 2008-10-23 | 2011-01-20 | Pacesetter, Inc. | Systems and methods for reducing lead heating and the risks of mri-induced stimulation |
US20100106227A1 (en) * | 2008-10-23 | 2010-04-29 | Pacesetter, Inc. | Systems and Methods for Disconnecting Electrodes of Leads of Implantable Medical Devices During an MRI to Reduce Lead Heating |
US8301249B2 (en) * | 2008-10-23 | 2012-10-30 | Pacesetter, Inc. | Systems and methods for exploiting the tip or ring conductor of an implantable medical device lead during an MRI to reduce lead heating and the risks of MRI-induced stimulation |
US20100138192A1 (en) * | 2008-12-01 | 2010-06-03 | Pacesetter, Inc. | Systems and Methods for Selecting Components for Use in RF Filters Within Implantable Medical Device Leads Based on Inductance, Parasitic Capacitance and Parasitic Resistance |
US8644951B1 (en) | 2009-12-02 | 2014-02-04 | University Of Central Florida Research Foundation, Inc. | Medical devices having MRI compatible metal alloys |
US8231980B2 (en) * | 2008-12-03 | 2012-07-31 | Boston Scientific Scimed, Inc. | Medical implants including iridium oxide |
WO2010078552A1 (en) * | 2009-01-05 | 2010-07-08 | Kenergy, Inc. | Mri compatible electrical lead for an implantable electronic medical device |
JP5389947B2 (en) | 2009-02-19 | 2014-01-15 | 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 providing arrhythmia therapy in an MRI environment |
WO2010101901A2 (en) * | 2009-03-02 | 2010-09-10 | Boston Scientific Scimed, Inc. | Self-buffering medical implants |
US8071156B2 (en) * | 2009-03-04 | 2011-12-06 | Boston Scientific Scimed, Inc. | Endoprostheses |
DE112010001330T5 (en) * | 2009-03-26 | 2012-02-16 | Kenergy Inc. | MRI-compatible implantable connection electrode interface |
US8478423B2 (en) * | 2009-04-07 | 2013-07-02 | Boston Scientific Neuromodulation Corporation | Insulator layers for leads of implantable electric stimulation systems and methods of making and using |
US20100274352A1 (en) * | 2009-04-24 | 2010-10-28 | Boston Scientific Scrimed, Inc. | Endoprosthesis with Selective Drug Coatings |
US8287937B2 (en) * | 2009-04-24 | 2012-10-16 | Boston Scientific Scimed, Inc. | Endoprosthese |
CN102326202A (en) * | 2009-06-30 | 2012-01-18 | 富士通先端科技株式会社 | Magnetic card reader |
US20110022158A1 (en) * | 2009-07-22 | 2011-01-27 | Boston Scientific Scimed, Inc. | Bioerodible Medical Implants |
US20110034983A1 (en) * | 2009-08-07 | 2011-02-10 | Pacesetter, Inc. | Implantable medical device lead incorporating a conductive sheath surrounding insulated coils to reduce lead heating during mri |
US8170687B2 (en) * | 2009-08-07 | 2012-05-01 | Pacesetter, Inc. | Implantable medical device lead incorporating insulated coils formed as inductive bandstop filters to reduce lead heating during MRI |
US8406897B2 (en) * | 2009-08-19 | 2013-03-26 | Boston Scientific Neuromodulation Corporation | Systems and methods for disposing one or more layers of material between lead conductor segments of electrical stimulation systems |
WO2011071597A1 (en) | 2009-12-08 | 2011-06-16 | Cardiac Pacemakers, Inc. | Implantable medical device with automatic tachycardia detection and control in mri environments |
US20110198118A1 (en) * | 2010-02-17 | 2011-08-18 | Ta Ya Electric Wire & Cable Co., Ltd. | Magnet wire |
US8668732B2 (en) * | 2010-03-23 | 2014-03-11 | Boston Scientific Scimed, Inc. | Surface treated bioerodible metal endoprostheses |
US8426734B2 (en) * | 2010-06-28 | 2013-04-23 | Ametek, Inc. | Low noise ECG cable and electrical assembly |
US8834657B2 (en) | 2010-08-20 | 2014-09-16 | Kenergy, Inc. | Method of manufacturing an mri compatible conductive lead body |
CN103282280B (en) | 2010-10-27 | 2016-02-10 | 洲际大品牌有限责任公司 | The accommodating packaging of the closeable product of magnetic |
WO2012067713A1 (en) * | 2010-11-18 | 2012-05-24 | Cardiac Pacemakers, Inc. | Insulative structure for mri compatible leads |
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 |
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 |
US10596369B2 (en) | 2011-03-01 | 2020-03-24 | Greatbatch Ltd. | Low equivalent series resistance RF filter for an active implantable medical device |
US9427596B2 (en) | 2013-01-16 | 2016-08-30 | 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 |
US10272252B2 (en) | 2016-11-08 | 2019-04-30 | Greatbatch Ltd. | Hermetic terminal for an AIMD having a composite brazed conductive lead |
CN103717130B (en) * | 2011-05-20 | 2016-09-07 | 佛罗里达中央大学研究基金会 | For finishing to the response of electromagnetic field through surface modified material |
USRE46699E1 (en) | 2013-01-16 | 2018-02-06 | Greatbatch Ltd. | Low impedance oxide resistant grounded capacitor for an AIMD |
AU2014315377B2 (en) * | 2013-09-06 | 2016-11-10 | Boston Scientific Neuromodulation Corporation | Systems and methods for reducing electromagnetic field-induced heating from an implantable pulse generator |
EP3104933A1 (en) | 2014-02-11 | 2016-12-21 | Cardiac Pacemakers, Inc. | Rf shield for an implantable lead |
US9782581B2 (en) | 2014-06-27 | 2017-10-10 | Boston Scientific Neuromodulation Corporation | Methods and systems for electrical stimulation including a shielded sheath |
US9782582B2 (en) | 2015-03-27 | 2017-10-10 | Boston Scientific Neuromodulation Corporation | Systems and methods for making and using electrical stimulation systems to reduce RF-induced tissue heating |
JP2016197510A (en) * | 2015-04-02 | 2016-11-24 | 日立金属株式会社 | Magnetic shield element wire, method for producing the same, and magnetic shield braid sleeve and magnetic shield cable using the same |
WO2016176645A1 (en) | 2015-04-30 | 2016-11-03 | Boston Scientific Neuromodulation Corporation | Electrical stimulation leads and systems having a rf shield along at least the lead and methods of making and using |
US9911559B2 (en) * | 2016-01-29 | 2018-03-06 | Microsoft Technology Licensing, Llc | Magnetically aligned circuit |
US9820418B1 (en) * | 2016-03-24 | 2017-11-14 | Jose Machado | Electromagnetic contamination neutralization composition, device, and method |
US10980979B2 (en) * | 2016-05-13 | 2021-04-20 | Becton, Dickinson And Company | Magnetic shield for medical devices |
US10249415B2 (en) | 2017-01-06 | 2019-04-02 | 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 |
Citations (21)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3901741A (en) * | 1973-08-23 | 1975-08-26 | Gen Electric | Permanent magnets of cobalt, samarium, gadolinium alloy |
US4166263A (en) * | 1977-10-03 | 1979-08-28 | Hitachi Metals, Ltd. | Magnetic core assembly for magnetizing columnar permanent magnet for use in electrostatic developing apparatus |
US4168481A (en) * | 1977-10-05 | 1979-09-18 | Hitachi Metals, Ltd. | Core assembly for magnetizing columnar permanent magnet for use in an electrostatic developing apparatus |
US4169998A (en) * | 1977-10-03 | 1979-10-02 | Hitachi Metals, Ltd. | Iron core assembly for magnetizing columnar permanent magnets for use in electrostatic developing apparatus |
US4180600A (en) * | 1975-10-23 | 1979-12-25 | Nathan Feldstein | Process using activated electroless plating catalysts |
US4631613A (en) * | 1984-04-16 | 1986-12-23 | Eastman Kodak Company | Thin film head having improved saturation magnetization |
US4705613A (en) * | 1984-04-16 | 1987-11-10 | Eastman Kodak Company | Sputtering method of making thin film head having improved saturation magnetization |
US4705353A (en) * | 1983-03-28 | 1987-11-10 | Schlumberger Technology Corporation | Optical fiber cable construction |
US4778714A (en) * | 1985-10-11 | 1988-10-18 | Minnesota Mining And Manufacturing Company | Nonabrasive magnetic recording tape |
US4963291A (en) * | 1988-06-13 | 1990-10-16 | Bercaw Robert M | Insulating electromagnetic shielding resin composition |
US5213851A (en) * | 1990-04-17 | 1993-05-25 | Alfred University | Process for preparing ferrite films by radio-frequency generated aerosol plasma deposition in atmosphere |
US5260132A (en) * | 1988-10-31 | 1993-11-09 | Hitachi Maxell, Ltd. | Acicular alloy magnetic powder |
US5315365A (en) * | 1992-06-17 | 1994-05-24 | Laser Precision Corp. | Macrobend splice loss tester for fiber optic splices with silicon gel cushion on optical coupling blocks |
US5540959A (en) * | 1995-02-21 | 1996-07-30 | Howard J. Greenwald | Process for preparing a coated substrate |
US5543070A (en) * | 1994-03-31 | 1996-08-06 | Mitsubishi Materials Corporation | Magnetic recording powder having low curie temperature and high saturation magnetization |
US5667924A (en) * | 1996-02-14 | 1997-09-16 | Xerox Corporation | Superparamagnetic image character recognition compositions and processes of making and using |
US5889091A (en) * | 1996-01-11 | 1999-03-30 | Xerox Corporation | Magnetic nanocompass compositions and processes for making and using |
US5913005A (en) * | 1997-01-29 | 1999-06-15 | Sumitomo Electric Industries, Ltd. | Single-mode optical fiber |
US5946439A (en) * | 1996-12-12 | 1999-08-31 | Sumitomo Electric Industries, Ltd. | Single-mode optical fiber |
US6072930A (en) * | 1998-11-04 | 2000-06-06 | Syracuse University | Method of fabricating a cylindrical optical fiber containing a particulate optically active film |
US6506972B1 (en) * | 2002-01-22 | 2003-01-14 | Nanoset, Llc | Magnetically shielded conductor |
Family Cites Families (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US5452720A (en) * | 1990-09-05 | 1995-09-26 | Photoelectron Corporation | Method for treating brain tumors |
US6102885A (en) * | 1996-08-08 | 2000-08-15 | Bass; Lawrence S. | Device for suction-assisted lipectomy and method of using same |
US5927621A (en) * | 1997-07-10 | 1999-07-27 | Xerox Corporation | Particle size reduction process |
JPH1186641A (en) * | 1997-09-10 | 1999-03-30 | Hitachi Metals Ltd | Cable |
US6225565B1 (en) * | 1999-06-07 | 2001-05-01 | The Untied States Of America As Represented By The Secretary Of The Navy | Flexible cable providing EMI shielding |
US6768053B1 (en) * | 2002-01-09 | 2004-07-27 | Nanoset, Llc | Optical fiber assembly |
WO2003061755A2 (en) * | 2002-01-22 | 2003-07-31 | Nanoset, Llc | Nanomagnetically shielded substrate |
-
2002
- 2002-01-22 US US10/054,407 patent/US6506972B1/en not_active Expired - Fee Related
- 2002-03-04 US US10/090,553 patent/US6930242B1/en not_active Expired - Fee Related
- 2002-08-26 US US10/229,183 patent/US6876886B1/en not_active Expired - Fee Related
- 2002-09-30 US US10/260,247 patent/US6673999B1/en not_active Expired - Fee Related
-
2005
- 2005-03-21 US US11/085,415 patent/US20050182471A1/en not_active Abandoned
Patent Citations (21)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3901741A (en) * | 1973-08-23 | 1975-08-26 | Gen Electric | Permanent magnets of cobalt, samarium, gadolinium alloy |
US4180600A (en) * | 1975-10-23 | 1979-12-25 | Nathan Feldstein | Process using activated electroless plating catalysts |
US4166263A (en) * | 1977-10-03 | 1979-08-28 | Hitachi Metals, Ltd. | Magnetic core assembly for magnetizing columnar permanent magnet for use in electrostatic developing apparatus |
US4169998A (en) * | 1977-10-03 | 1979-10-02 | Hitachi Metals, Ltd. | Iron core assembly for magnetizing columnar permanent magnets for use in electrostatic developing apparatus |
US4168481A (en) * | 1977-10-05 | 1979-09-18 | Hitachi Metals, Ltd. | Core assembly for magnetizing columnar permanent magnet for use in an electrostatic developing apparatus |
US4705353A (en) * | 1983-03-28 | 1987-11-10 | Schlumberger Technology Corporation | Optical fiber cable construction |
US4631613A (en) * | 1984-04-16 | 1986-12-23 | Eastman Kodak Company | Thin film head having improved saturation magnetization |
US4705613A (en) * | 1984-04-16 | 1987-11-10 | Eastman Kodak Company | Sputtering method of making thin film head having improved saturation magnetization |
US4778714A (en) * | 1985-10-11 | 1988-10-18 | Minnesota Mining And Manufacturing Company | Nonabrasive magnetic recording tape |
US4963291A (en) * | 1988-06-13 | 1990-10-16 | Bercaw Robert M | Insulating electromagnetic shielding resin composition |
US5260132A (en) * | 1988-10-31 | 1993-11-09 | Hitachi Maxell, Ltd. | Acicular alloy magnetic powder |
US5213851A (en) * | 1990-04-17 | 1993-05-25 | Alfred University | Process for preparing ferrite films by radio-frequency generated aerosol plasma deposition in atmosphere |
US5315365A (en) * | 1992-06-17 | 1994-05-24 | Laser Precision Corp. | Macrobend splice loss tester for fiber optic splices with silicon gel cushion on optical coupling blocks |
US5543070A (en) * | 1994-03-31 | 1996-08-06 | Mitsubishi Materials Corporation | Magnetic recording powder having low curie temperature and high saturation magnetization |
US5540959A (en) * | 1995-02-21 | 1996-07-30 | Howard J. Greenwald | Process for preparing a coated substrate |
US5889091A (en) * | 1996-01-11 | 1999-03-30 | Xerox Corporation | Magnetic nanocompass compositions and processes for making and using |
US5667924A (en) * | 1996-02-14 | 1997-09-16 | Xerox Corporation | Superparamagnetic image character recognition compositions and processes of making and using |
US5946439A (en) * | 1996-12-12 | 1999-08-31 | Sumitomo Electric Industries, Ltd. | Single-mode optical fiber |
US5913005A (en) * | 1997-01-29 | 1999-06-15 | Sumitomo Electric Industries, Ltd. | Single-mode optical fiber |
US6072930A (en) * | 1998-11-04 | 2000-06-06 | Syracuse University | Method of fabricating a cylindrical optical fiber containing a particulate optically active film |
US6506972B1 (en) * | 2002-01-22 | 2003-01-14 | Nanoset, Llc | Magnetically shielded conductor |
Cited By (53)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20050222657A1 (en) * | 2004-03-30 | 2005-10-06 | Wahlstrand Carl D | MRI-safe implantable lead |
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 |
US7844343B2 (en) | 2004-03-30 | 2010-11-30 | Medtronic, Inc. | 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 |
US9302101B2 (en) | 2004-03-30 | 2016-04-05 | Medtronic, Inc. | MRI-safe implantable lead |
US8989840B2 (en) | 2004-03-30 | 2015-03-24 | Medtronic, Inc. | Lead electrode for use in an MRI-safe implantable medical device |
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 |
US8670840B2 (en) | 2006-11-30 | 2014-03-11 | Cardiac Pacemakers, Inc. | RF rejecting lead |
US10398893B2 (en) | 2007-02-14 | 2019-09-03 | Medtronic, Inc. | Discontinuous conductive filler polymer-matrix composites for electromagnetic shielding |
US10537730B2 (en) | 2007-02-14 | 2020-01-21 | Medtronic, Inc. | Continuous conductive materials 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 |
US8731685B2 (en) * | 2007-12-06 | 2014-05-20 | Cardiac Pacemakers, Inc. | Implantable lead having a variable coil conductor pitch |
US20090149933A1 (en) * | 2007-12-06 | 2009-06-11 | Cardiac Pacemakers, Inc. | Implantable lead having a variable coil conductor pitch |
US8666508B2 (en) | 2008-02-06 | 2014-03-04 | Cardiac Pacemakers, Inc. | Lead with MRI compatible design features |
US9731119B2 (en) | 2008-03-12 | 2017-08-15 | Medtronic, Inc. | System and method for implantable medical device lead shielding |
US8688236B2 (en) | 2008-05-09 | 2014-04-01 | Cardiac Pacemakers, Inc. | Medical lead coil conductor with spacer element |
US9084883B2 (en) | 2009-03-12 | 2015-07-21 | Cardiac Pacemakers, Inc. | Thin profile conductor assembly for medical device leads |
US20100234929A1 (en) * | 2009-03-12 | 2010-09-16 | Torsten Scheuermann | Thin profile conductor assembly for medical device leads |
US9186499B2 (en) | 2009-04-30 | 2015-11-17 | Medtronic, Inc. | Grounding 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 |
US10035014B2 (en) | 2009-04-30 | 2018-07-31 | Medtronic, Inc. | Steering an implantable medical lead via a rotational coupling to a stylet |
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 |
US9272136B2 (en) | 2009-04-30 | 2016-03-01 | Medtronic, Inc. | Grounding of a shield within an implantable medical lead |
US9452284B2 (en) | 2009-04-30 | 2016-09-27 | Medtronic, Inc. | Termination of a shield within an implantable medical lead |
US9205253B2 (en) | 2009-04-30 | 2015-12-08 | Medtronic, Inc. | Shielding an implantable medical lead |
US9216286B2 (en) | 2009-04-30 | 2015-12-22 | Medtronic, Inc. | Shielded implantable medical lead with guarded termination |
US9220893B2 (en) | 2009-04-30 | 2015-12-29 | Medtronic, Inc. | Shielded implantable medical lead with reduced torsional stiffness |
US8744600B2 (en) | 2009-06-26 | 2014-06-03 | Cardiac Pacemakers, Inc. | Medical device lead including a unifilar coil with improved torque transmission capacity and reduced MRI heating |
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 |
US9199077B2 (en) | 2009-12-31 | 2015-12-01 | Cardiac Pacemakers, Inc. | MRI conditionally safe lead with multi-layer conductor |
US8676351B2 (en) | 2009-12-31 | 2014-03-18 | Cardiac Pacemakers, Inc. | MRI conditionally safe lead with low-profile multi-layer conductor for longitudinal expansion |
US8798767B2 (en) | 2009-12-31 | 2014-08-05 | Cardiac Pacemakers, Inc. | MRI conditionally safe lead with multi-layer conductor |
US9050457B2 (en) | 2009-12-31 | 2015-06-09 | Cardiac Pacemakers, Inc. | MRI conditionally safe lead with low-profile conductor for longitudinal expansion |
US8825181B2 (en) | 2010-08-30 | 2014-09-02 | Cardiac Pacemakers, Inc. | Lead conductor with pitch and torque control for MRI conditionally safe use |
US8666512B2 (en) | 2011-11-04 | 2014-03-04 | Cardiac Pacemakers, Inc. | Implantable medical device lead including inner coil reverse-wound relative to shocking coil |
US9463317B2 (en) | 2012-04-19 | 2016-10-11 | Medtronic, Inc. | Paired medical lead bodies with braided conductive shields having different physical parameter values |
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 |
US9333344B2 (en) | 2012-06-01 | 2016-05-10 | 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 |
US9504822B2 (en) | 2012-10-18 | 2016-11-29 | Cardiac Pacemakers, Inc. | Inductive element for providing MRI compatibility in an implantable medical device lead |
US8983623B2 (en) | 2012-10-18 | 2015-03-17 | Cardiac Pacemakers, Inc. | Inductive element for providing MRI compatibility in an implantable medical device lead |
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 |
US9682231B2 (en) | 2014-02-26 | 2017-06-20 | Cardiac Pacemakers, Inc. | Construction of an MRI-safe tachycardia lead |
US9504821B2 (en) | 2014-02-26 | 2016-11-29 | Cardiac Pacemakers, Inc. | Construction of an MRI-safe tachycardia 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 |
Also Published As
Publication number | Publication date |
---|---|
US6506972B1 (en) | 2003-01-14 |
US6930242B1 (en) | 2005-08-16 |
US6876886B1 (en) | 2005-04-05 |
US6673999B1 (en) | 2004-01-06 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US6876886B1 (en) | Magnetically shielded conductor | |
US6906256B1 (en) | Nanomagnetic shielding assembly | |
US6971391B1 (en) | Protective assembly | |
US20050247472A1 (en) | Magnetically shielded conductor | |
US6844492B1 (en) | Magnetically shielded conductor | |
US7162302B2 (en) | Magnetically shielded assembly | |
US6846985B2 (en) | Magnetically shielded assembly | |
US7127294B1 (en) | Magnetically shielded assembly | |
US6980865B1 (en) | Implantable shielded medical device | |
US7091412B2 (en) | Magnetically shielded assembly | |
US7473843B2 (en) | Magnetic resonance imaging coated assembly | |
US6765144B1 (en) | Magnetic resonance imaging coated assembly | |
US8788058B2 (en) | Leads with high surface resistance | |
US5827186A (en) | Method and PDT probe for minimizing CT and MRI image artifacts | |
US7493167B2 (en) | Magnetically shielded AIMD housing with window for magnetically actuated switch | |
EP2125103B1 (en) | Continuous conductive materials for electromagnetic shielding | |
WO2009076169A2 (en) | Implantable lead with shielding | |
EP2520334A1 (en) | Magnetic stimulation using plasma |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AS | Assignment |
Owner name: NANOSET, LLC, NEW YORK Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:WANG, XINGWU;REEL/FRAME:016413/0373 Effective date: 20050311 |
|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |
|
AS | Assignment |
Owner name: BIOPHAN TECHNOLOGIES, INC., NEW YORK Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:NANOSET, LLC;REEL/FRAME:020635/0205 Effective date: 20080215 |