WO2001037926A1 - Appareil pour le transfert d'energie au-dela d'une limite - Google Patents

Appareil pour le transfert d'energie au-dela d'une limite Download PDF

Info

Publication number
WO2001037926A1
WO2001037926A1 PCT/US2000/031923 US0031923W WO0137926A1 WO 2001037926 A1 WO2001037926 A1 WO 2001037926A1 US 0031923 W US0031923 W US 0031923W WO 0137926 A1 WO0137926 A1 WO 0137926A1
Authority
WO
WIPO (PCT)
Prior art keywords
area
approximately
winding
inches
energy
Prior art date
Application number
PCT/US2000/031923
Other languages
English (en)
Inventor
Farhad Zarinetchi
Original Assignee
Abiomed, Inc.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Abiomed, Inc. filed Critical Abiomed, Inc.
Priority to EP00978846A priority Critical patent/EP1231981A1/fr
Publication of WO2001037926A1 publication Critical patent/WO2001037926A1/fr

Links

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
    • A61N1/372—Arrangements in connection with the implantation of stimulators
    • A61N1/378—Electrical supply
    • A61N1/3787—Electrical supply from an external energy source

Definitions

  • the present invention relates to energy transfer methods and devices, and more particularly, to transmitting energy from a position on one side of a boundary and receiving energy at a position on another side of a boundary, wherein the energy received is not significantly affected by more than nominal changes in the relative transmitting and receiving positions.
  • one or more devices that require power may be located within the confines of a closed system, or "body, " ' in which it may be difficult and/or undesirable to also include a power source.
  • the closed system or body may be delimited by various types of boundaries, and the system internal to the boundary may be living or inanimate, may perform a variety of functions, and may have a variety of operational and physical requirements and/or constraints. In some cases, such requirements and constraints may make the implementation of an "internal" power source for internally located devices problematic.
  • an internal power source such as a battery
  • a battery is capable of providing power only for a finite time period, after which the battery must be changed or recharged. Accordingly, entry into the system would likely be required to change or recharge the battery.
  • significant internal power requirements and a limited internal space may prohibit the implementation of a suitably sized internal power source.
  • contamination and/or security issues may pose particular challenges in implementing an internal power source.
  • a power source external to the system and some feasible means of transferring power from the external source to one or more internal devices may be preferable in some applications.
  • a closed system is the human body.
  • a variety of prosthetic and other devices that require power may be surgically implanted within various portions of the body.
  • Some examples of such devices include a synthetic replacement heart, a circulatory blood pump or ventricular assist device (VAD), a cochlear (ear) implant, a pacemaker, and the like.
  • VAD circulatory blood pump or ventricular assist device
  • ear cochlear
  • pacemaker pacemaker
  • TET transcutaneous energy transfer'
  • a transformer that includes a primary winding (or coil) external to the body and a secondary winding internal to the body. Both the primary and secondary windings generally have essentially planar (flat) geometries, typically are circular in shape, and are placed proximate to respective outer and inner layers of a patient ' s skin; hence, the term “transcutaneous'” commonly refers to energy transfer "through the skin.'” Energy is transferred from the primary winding to the secondary winding in the form of a magnetic field.
  • the implanted secondary winding converts the transferred energy in the magnetic field to electrical power for the implanted device, which acts as a "load" on the secondary winding.
  • TET devices differ from conventional power transformers in that power transformers typically include a magnetic core around which the primary and secondary windings are wound. The magnetic core provides a "low resistance" path (a low reluctance magnetic circuit) for the magnetic field to travel between the primary and secondary windings.
  • the energy (or power) transfer efficiency of a transformer is related to the reluctance of the magnetic circuit through which the magnetic field travels.
  • the reluctance of the magnetic circuit in turn is a function of the material through which the magnetic field passes from the primary to the secondary windings (e.g., a magnetic core) and the relative arrangement and spatial positioning of the windings relative to each other.
  • a low reluctance magnetic circuit including a magnetic core that structurally couples the primary and secondary windings, as in a conventional power transformer, provides for a high energy transfer efficiency.
  • One potential problem associated with transferring energy across a boundary is that structurally coupling the primary and secondary windings (e.g., via a magnetic core) may be difficult or impossible.
  • structurally coupling the primary and secondary windings e.g., via a magnetic core
  • the nature of the application in the human body i.e., the respective external and internal locations of the transformer windings
  • the magnetic field generated by the primary winding must travel to the secondary winding through the skin and perhaps other body tissues, which typically are less magnetically "permeable" than a magnetic core.
  • conventional TET devices generally have a relatively lower energy transfer efficiency.
  • one focus of conventional TET device designs primarily has been on maintaining an optimum magnetic coupling between the primary and secondary windings, based on the physical arrangement and spatial positioning of the windings relative to each other.
  • a measure of magnetic coupling between the windings typically is expressed as a mutual inductance or a coupling coefficient.
  • magnetic coupling between the windings increases as the windings are spatially aligned such that the secondary winding intercepts a larger portion of the magnetic field generated by the primary winding.
  • magnetic coupling between the windings generally increases as the distance separating the windings decreases.
  • conventional TET device designs generally have involved similarly-sized mutually-aligned windings separated by a small distance.
  • the size of transformer windings practically may be constrained by limitations imposed by the system in which they are implemented.
  • the size of the windings in such devices generally is constrained by various physical limitations of the human body.
  • attempts at optimizing magnetic coupling in conventional TET device designs generally are limited to selecting the largest practical size for the secondary winding, and then selecting an identical size for the primary winding.
  • practical winding sizes of conventional TET devices for human applications typically have been limited to less than approximately three inches (75 mm) in diameter.
  • an "effective operating range" i.e., the axial distance through the skin that separates the primary and secondary windings
  • an "effective operating range" of conventional TET devices generally is limited to less than .5 inches (5-10 mm).
  • Implanted prostheses or other devices and particularly an implanted device that performs a life-sustaining function, generally must have a consistent source of available power. Without a consistent power source, the implanted device may function erratically or intermittently. Such erratic or intermittent operation can have undesirable and. in some cases. serious life-threatening effects on the patient.
  • the need for consistent power practically constrains both the axial distance that separates the primary and secondary windings as well as the alignment of the windings in a conventional TET device during normal "use.”
  • Such constraints present a disadvantage to the patient, whose mobility may be substantially limited so as to prevent shifting and misalignment between the windings.
  • such constraints may preclude the use of ointments or bandages in connection with the TET device, which may add to the axial displacement between the windings, and may also preclude the use of the TET device through clothing, which may exacerbate both lateral and axial shifting between the windings with patient movement.
  • an apparatus of the invention comprises a first energy transfer element to transmit energy and a second energy transfer element to receive at least a portion of the energy.
  • the first energy transfer element delimits a first area through which the energy is transmitted
  • the second energy transfer element delimits a second area through which at least a portion of the energy is received as received energy.
  • the first area delimited by the first energy transfer element is at least twice as large as the second area delimited by the second energy transfer element.
  • an apparatus of the invention comprises a first energy transfer element to transmit energy, the first energy transfer element located at a first position on a first side of a boundary, and a second energy transfer element located at a second position on a second side of a boundary to receive at least a portion of the energy transmitted by the first energy transfer element as received energy.
  • the first and second energy transfer elements are constructed and arranged such that the received energy is not significantly affected by a more than nominal change in at least one of the first position and the second position.
  • a method of the invention for transferring energy comprises acts of a) transmitting the energy from a first area having a first position on a first side of a boundary, and b) receiving at least a portion of the energy as received energy in a second area having a second position on a second side of the boundary.
  • the first and second areas are respectively dimensioned and aligned such that the received energy is not significantly affected by a more than nominal change in at least one of the first and second positions.
  • a transcutaneous power transformer of the invention comprises a primary winding located external to a body to generate a first magnetic flux, and a secondary winding located internal to the body and positioned relative to the primary winding so as to receive at least a portion of the first magnetic flux as a second magnetic flux.
  • the primary winding and the secondary winding are constructed and arranged such that the secondary winding is capable of providing a load with a sufficient power based upon the second magnetic flux, irrespective of a significant spatial displacement of at least one of the primary winding and the secondary winding.
  • a transcutaneous energy transfer apparatus of the invention comprises a primary coil located external to a body to transmit a magnetic field and a secondary coil located internal to the body to receive at least a portion of the magnetic field.
  • the primary coil and the secondary coil are constructed and arranged such that a magnetic coupling between the primary coil and the secondary coil is significantly insensitive to a more than nominal spatial displacement of at least one of the primary coil and the secondary coil.
  • a primary winding of the invention for use in a transcutaneous energy device the transcutaneous energy device comprising the primary winding and a secondary winding, comprises at least one winding turn to transmit energy based on an electrical signal applied to the winding turn.
  • the primary winding delimits a first area through which the energy is transmitted, wherein the first area is at least twice as large as a second area delimited by the secondary winding.
  • a primary winding of the invention for use in a transcutaneous energy device comprises at least one winding turn to transmit energy based on an electrical signal applied to the winding turn.
  • the primary winding delimits a first area through which the energy is transmitted, wherein the first area is at least approximately 9.7 square inches.
  • Fig. 1 is a diagram showing an example of an implementation of an energy transfer device in a human body, according to one embodiment of the invention:
  • Fig. 2 is a diagram showing a more detailed side view of the energy transfer device shown in Fig. 1. according to one embodiment of the invention
  • Fig. 3 is a diagram showing a more detailed top view of the energy transfer device shown in Fig. 1, according to one embodiment of the invention
  • Fig. 4 is a diagram similar to Fig. 3, showing a top view of an energy transfer device according to another embodiment of the invention
  • Fig. 5 is a diagram showing a three-dimensional view of a winding used in an energy transfer device according to one embodiment of the invention, and the effect of winding geometry on magnetic field;
  • Fig. 6 is a diagram showing a two-dimensional view of the winding of Fig. 5, and the magnetic field in greater detail
  • Fig. 7 is a graph comparing the relative magnetic field strength at various normal or axial distances from a winding for two differently sized windings similar to that shown in Fig. 5;
  • Fig. 8 is a graph similar to Fig. 7 comparing the relative magnetic field strength at various lateral distances from an axis of a winding for two differently sized windings;
  • Fig. 9 is a diagram showing a three-dimensional view of the energy transfer device of
  • Fig. 10 is a diagram showing the energy transfer device of Fig. 9. with a secondary winding of the device laterally displaced;
  • Fig. 11 is a diagram showing a more detailed two-dimensional view of the energy transfer device of Fig. 9, according to one embodiment of the invention.
  • One embodiment of the present invention is directed to methods and apparatus for transferring energy across a boundary, for example, from a position external to a closed system, or "body,” to a position internal to the body.
  • the transferred energy may be used to provide power to a device located internal to the body.
  • the energy received internal to the body, and hence the power provided to the internal device is not significantly affected by appreciable changes in the relative positions between an external energy transmitter and an internal energy receiver on opposite sides of a boundary.
  • more than nominal (or trivial) axial or lateral displacements of one or both of the energy transmitter and receiver do not result in significant variations in the power provided to the internal device.
  • a sufficiently stable power may be provided to the internal device, notwithstanding more than nominal movement of one or both of the energy transmitter and the energy receiver.
  • Another aspect of the present invention relates to energy transfer methods and devices for use in connection with the human body.
  • one embodiment of the invention is directed to a transcutaneous energy transfer (TET) device functioning as a power transformer to transfer power from an external power source to a device implanted in the body.
  • TET transcutaneous energy transfer
  • a TET device in one aspect of this embodiment, includes an "oversized" primary winding (coil) affixed in proximity to an exterior surface of the skin, and a secondary winding implanted in the body and aligned with the primary winding. More specifically, according to this embodiment, an area delimited by the primary winding, from which a magnetic field is generated, is at least twice that of an area delimited by the secondary winding of the TET device, through which the secondary winding intercepts or "receives" the magnetic field.
  • the larger area of the oversized primary winding allows a significant displacement between the primary and secondary windings while nonetheless maintaining uniformity of the magnetic field that impinges on the secondary winding.
  • the secondary winding is capable of providing a sufficiently stable power to the implanted device, notwithstanding more than nominal shifts in the relative positions of the windings.
  • an oversized primary winding in a TET device according to one embodiment of the present invention increases the magnetic field strength at a given axial distance from the primary winding, relative to that of a primary winding having the same or nearly the same size as the secondary winding.
  • the larger area of the oversized primary winding from which the magnetic field is generated permits a more than nominal lateral displacement or misalignment of the secondary winding relative to the primary winding, while nonetheless preserving the uniformity of the magnetic field that impinges on the secondary winding.
  • the increased strength and area of the magnetic field due to an oversized primary winding increases an "effective operating range" (maximum axial and/or lateral displacement while maintaining a sufficient power output to a load) of a TET device according to one embodiment of the invention as compared to conventional TET devices.
  • the increased effective operating range due to the oversized primary winding may permit, for example, a TET device according to the invention to be used through various objects such as clothing, creams, bandages, medicated ointments, and the like, even though such objects may add appreciably to the distance separating the primary and secondary windings and the degree of shifting that may occur between the windings with patient movement. As a result, a greater degree of patient comfort and flexibility may be afforded by methods and apparatus according to the invention.
  • an oversized primary winding may decrease the magnetic coupling in a TET device according to the invention relative to that of a conventional TET device having similarly-sized windings
  • such a reduction in magnetic coupling may be compensated in part by configuring the primary and secondary windings as "tuned" circuits. In such a configuration, energy is transferred from the primary winding to the secondary winding at or near a resonant frequency of the tuned circuits.
  • This arrangement can result in a TET device having an energy transfer efficiency (power output/power input) between approximately 75-80%.
  • the primary and secondary windings may be axially or laterally displaced from “typical" operating positions by up to two inches (50 mm), and the secondary winding is nonetheless able to deliver to a load at least 50% of the power capability of the TET device in the typical position.
  • Fig. 1 is a diagram showing an example of an implementation of a TET device 100 in a human body 90. according to one embodiment of the invention.
  • the TET device 100 is employed to transfer energy (or power) from a power source 112 located externally to the body 90 (e.g.. strapped to the waist of the patient) to one or more implanted devices 110 internal to the body 90.
  • An implanted device 1 10 that receives power from the TET device 100 may be, for example, an implanted prosthesis such as a synthetic heart or a circulatory blood pump.
  • an implanted device 110 may be a battery that receives power from the TET device 100, for example, to maintain a charge on.the battery or to recharge the battery. The implanted battery in turn provides power to one or more implanted prosthesis or other implanted devices.
  • a primary winding 102 of the TET device 100 is positioned externally proximate to the skin 302 of the patient and connected to the power source 1 12 via a cable 104.
  • a secondary winding 106 of the TET device 100 is implanted within the body 90 of the patient and is connected to the implanted device 1 10 by a cable 108. Both the internal secondary winding 106 and the implanted device 1 10 are shown shaded in
  • the primary winding 102 and the secondary winding 106 are constructed and arranged such that at least a portion of a magnetic field generated by the primary winding 102 travels through the skin 302 (and perhaps other body tissues or coverings) and impinges upon the secondary winding 106.
  • the portion of the magnetic field intercepted by the secondary winding 106 (and hence the received energy) is converted to an electrical power which is provided to the implanted device 1 10.
  • the implanted device 1 10 serves as a "load" for the secondary winding 106.
  • the primary winding 102 delimits a larger area than does the secondary winding 106.
  • Fig. 1 shows a “side " view of the TET device 100 shown in Fig. 1.
  • Fig. 2 viewed along the patient " s skin 302 (as if the patient were lying on their back, for example).
  • the skin 302 approximately defines an x-axis 14 in a Cartesian coordinate system.
  • Fig. 2 also shows a z-axis 12 essentially perpendicular to the skin 302. which serves as a common axis between the primary winding 102 and the secondary winding 106.
  • a y-axis 13 of the Cartesian coordinate system is directed through the page of Fig. 2, representing the direction of the side view. While the primary and secondary windings of Fig.
  • the windings are typically planar devices having nominal thicknesses. It should also be appreciated, however, that in other embodiments, one or both of the windings may have a significant dimension along the z-axis shown in Fig. 2, and have a variety of volumetric shapes and relative arrangements.
  • the secondary winding 106 may be affixed to a layer of tissue
  • the primary winding 102 may be placed directly on an external surface of the skin 302.
  • the primary winding 102 may be placed proximate to an external surface of the skin 302 above one or more intervening layers of material 103 which may be. for example, one or more articles of clothing, an ointment or a cream, one or more bandages, and the like.
  • Figs. 3 and 4 each is a "top" view (looking down onto the patient of Fig. 1) of an example of a TET device 100 that may be employed in the embodiment shown in Fig. 1.
  • the invention is not limited to the examples shown in Figs. 3 and 4, as these examples are merely for illustrative purposes.
  • the x-axis 14 and the y-axis 13 define a plane that is essentially parallel with the patient ' s skin 302.
  • the primary winding 102 delimits an approximately circular area 102' having a diameter 24 and a radius 202 (Ri), while the secondary winding 106 delimits an approximately circular area 106' having a diameter 26 and a radius 204 (R 2 ) which is smaller than the radius 202 (Ri).
  • the ratio of the area 102' to the area 106' in the example of Fig. 3 is given by (R ⁇ /R 2 ) " .
  • Fig. 3 also shows that, at an optimum relative position, the primary and secondary windings 102 and 106 are essentially "mutually aligned," in that they share a common geometric center through which the z-axis 12 (shown in Fig. 2) passes.
  • Fig. 4 shows a "top" view similar to Fig. 3 in which the primary winding 102 and the secondary winding 106 delimit areas 102' and 106'. respectively, having essentially square shapes. While the sides of the square areas shown in Fig. 4 are essentially parallel to the respective x and y-axes indicated in Fig. 4, it should be appreciated that one or both of the square shaped windings 102 and 106 may be oriented arbitrarily with respect to the x and y- axes shown in the figure.
  • the primary winding 102 has a side dimension 203 (a) and the secondary winding 106 has a side dimension 205 (b) that is smaller than the side dimension 203.
  • Fig. 4 shows that, at an optimum relative position, the primary and secondary windings 102 and 106 are essentially "mutually aligned.” in that they share a common geometric center through which the z-axis 12 (shown in Fig. 2) passes.
  • the first area 102' is at least twice that of the second area 106'.
  • a suitable ratio of the first area 102' to the second area 106' delimited by a TET device having arbitrary winding perimeter shapes is in a range of from approximately 2:1 to 80: 1.
  • the first area 102' may be from 2 to 80 times larger than the second area 106'.
  • the first area may be at least 4 times larger than the second area.
  • the first area may be at least 9 times larger than the second area, at least 16 times larger than the second area, at least 36 times larger than the second area, and at least 80 times larger than the second area.
  • the first area 102' may be in a range of from approximately 7 to 30 square inches and the second area 106' may be in a range of from approximately 2 to 7 square inches, as long as the ratio of the first area to the second area is at least 2: 1.
  • the first area 102' may have a diameter 24 in a range of from approximately 3 to 6 inches and the second area 106' may have a diameter 26 in a range of from approximately 1 to 3 inches. More specifically, according to one aspect of this embodiment, the first area 102' may have a diameter 24 in a range of from approximately 4 to 5.5 inches and the second area 106' may have a diameter 26 in a range of from approximately 2 to 2.75 inches.
  • the first area 102' may have a diameter 24 that is greater than 3.5 inches. In yet another embodiment, the first area 102' has a diameter of approximately 5.5 inches and the second area 106' has a diameter of approximately 2.5 inches.
  • examples of ratios of the diameter of the first area to the diameter of the second area suitable for purposes of embodiments of the invention involving essentially circular first and second areas include, but are not limited to. 1.5:1, 2:1, 3:1, 3.5: 1. 4:1, 6:1, and 9:1. The significance of the relative dimensions of the primary and secondary windings is discussed in greater detail further below. A brief discussion of magnetic field theory will facilitate a fuller understanding of the inventive concepts behind various aspects of the present invention. Fig.
  • FIG. 5 shows a three- dimensional view of the primary winding 102 of the TET device 100. in a Cartesian coordinate system defined by the x-axis 14. the y-axis 13, and the z-axis 12.
  • the primary winding 102 illustrated in Fig. 5 may be viewed as a generic example of a winding independent from the TET device 100, for purposes of explaining some principles of magnetic field theory.
  • the winding 102 of Fig. 5 is idealized to have a single winding turn to simplify the mathematical relationships discussed below. It should be appreciated, however, that windings according to various embodiments of the invention may have a number of winding turns. Nonetheless, the following discussion pertaining to a single turn winding is useful for illustrating some relevant concepts related to the present invention.
  • the winding 102 delimits an approximately circular area 102' which defines a plane 300.
  • the x-axis 14 and the y-axis 13 pass through the plane 300, and each of the x, y, and z-axes pass through a geometric center 10 of the area 102'.
  • the area 102' has a radius 202 (R).
  • a current 15 (/ ' ) flowing through the winding 102 creates a magnetic field H, represented in Fig. 5 as lines of magnetic flux 30, according to the relationship
  • Fig. 6 is a two-dimensional "side" view looking along the y-axis of Fig. 5. which shows in part that the magnetic field generated by the current / flowing through the winding 102 according to Eq. (1) may be represented by a series of approximately elliptically shaped concentric magnetic flux lines 30, having increasing diameters as the observation point increases in distance from the winding 102.
  • the magnetic flux lines 30 shown in Fig. 6 may be viewed as "straightening out” as one approaches the center of the area 102' delimited by the winding 102 (i.e., along the z-axis 12). which constitutes the farthest point within the area 102' from the current / flowing in the winding.
  • the magnetic field generated by the winding 102 within the area 102' can be viewed as a number of essentially straight magnetic flux lines 30 forming a cylindrical profile parallel to and surrounding the z- axis 12, as shown in Fig. 5.
  • Fig. 7 is a graph showing two plots 502 and 504 of relative magnetic field strength as a function of distance along the z-axis 12 from the plane 300 of the winding 102 shown in Figs. 5 and 6. for a given current / flowing through the single turn winding. For such an "axial" displacement from the winding plane 300 along the z-axis 12. Eq. (1) reduces to the relationship
  • FIG. 7 shows the horizontal axis of the graph in units of the radius R of a given winding.
  • the plot 502 in Fig. 7 represents Eq. (2) using a winding radius of R
  • the plot 504 represents Eq. (2) using a winding radius of 2R through which the same magnitude of current flows.
  • Fig. 7 compares the relative strengths of a magnetic field at an axial observation point from the plane of a winding, for two differently sized windings each having a single winding turn.
  • Fig. 7 also shows that at the same axial distance R. the relative magnetic field strength from a larger winding having a radius of 2R is approximately .7. as shown by the plot 504.
  • the graph of Fig. 7 demonstrates that by doubling the radius (or diameter) of a winding, the "effective axial operating range" may be in principle doubled, i.e., a larger winding area 102' provides a greater effective axial operating range relative to a smaller sized winding.
  • the horizontal axis of the graph of Fig. 8 refers to a lateral displacement along the x'-axis 14'. which is perpendicular to the z-axis 12 at a distance from the winding plane 300 equal to the radius R of the winding area 102'.
  • the plot 506 in the graph of Fig. 8 represents Eq. (1) evaluated at a number of observation points along the x'-axis. where the vector r in Eq.
  • Figs. 9 and 10 are more detailed three-dimensional diagrams of the TET device 100 shown in Figs. 1, 2, and 3, illustrating two different positions of the primary winding 102 relative to the secondary winding 106.
  • the primary winding 102 has an essentially planar shape and defines a first plane which includes the area 102' ("above" the skin 302). as indicated in Fig. 9 by the xi-axis 14 and the y-axis 13.
  • the Xi-axis and the y-axis intersect at a geometric center 10 of the primary winding 102. which serves as a reference for the position of the primary winding 102 in space.
  • the secondary winding 106 has an essentially planar shape and defines a second plane including the area 106' ("below" the skin 302).
  • a geometric center 20 of the secondary winding 106 serves as a reference for the position of the secondary winding in space.
  • An x 2 - axis 16 essentially parallel to the xj-axis 14 passes through the second plane defined by the secondary winding 106.
  • the primary and secondary windings are essentially parallel and are separated by a normal or axial distance 18 along the z-axis 12.
  • Fig. 9 shows an "optimum" alignment for the primary and secondary windings.
  • the respective positions of the primary winding 102 and the secondary winding 106, as indicated by their respective geometric centers 10 and 20. are such that the z-axis 12 serves as a common axis which passes through each geometric center; namely, in the example of Fig. 9 showing essentially circular windings, the primary winding 102 and the secondary winding 106 are concentrically aligned.
  • a distance corresponding to the difference between the respective radii 202 and 204 (Ri - R 2 ) of the primary and secondary windings is indicated in Fig. 9 by the reference character 25.
  • the primary winding 102 of the TET device 100 shown in Fig. 9 transmits energy in the form of magnetic field, which may be represented by a cylindrical profile of magnetic flux lines 30.
  • the secondary winding 106 intercepts (receives) at least a portion of the magnetic field transmitted by the primary winding 102.
  • the magnetic field (or energy) received by the secondary winding 106 is not significantly affected by a change in the normal (axial) distance 18 between the relative positions of the primary and secondary windings, wherein the change amounts to more than a nominal change in the axial distance 18.
  • an electrical power supplied by the secondary winding 106 is not significantly affected by a change in the normal (axial) distance 18 between the relative positions of the primary and secondary windings, wherein the change amounts to more than a nominal change in the axial distance 18.
  • a device receiving power from the secondary winding 106 e.g., the implanted device 1 10 shown in Fig. 1 .
  • the effective axial operating range of a given primary winding 102 is a function, in part, of the radius of the winding.
  • the radius of the primary winding 102 of Fig. 9 may be selected based in part upon a "typical" axial distance 18 expected during normal operation and use of the TET device 100 (e.g.. with a patient having an implanted device), and based on the degree of desired stability of power supplied by the secondary winding 106 as a result of some maximum expected change in the axial distance 18. using Eqs. (1) or (2) and the plots of Fig. 7 as a guideline.
  • the primary winding 102 and the secondary winding 106 may be constructed and a ⁇ anged such that sufficient power is provided by the secondary winding at a "typical" axial distance 18 of greater than approximately .25 inches (approximately 6 millimeters).
  • the secondary winding 106 may be constructed and arranged such that sufficient power is provided by the secondary winding at a "typical" axial distance 18 in a range of from approximately .5 to 1 inch (approximately 13-26 mm).
  • a "nominal” change in the axial distance refers to a minor axial displacement that amounts to less than approximately .15 inches (approximately 4 millimeters).
  • a “more than nominal” change in the typical axial distance refers to a change of greater than .15 inches in the axial distance.
  • a "more than nominal change " in the axial distance may be viewed in terms of an axial displacement that amounts to more than approximately 60-70%> of the typical axial distance. For example, using a typical axial distance of at least .25 inches for purposes of illustration, a change of at least .15 inches amounts to a 60%> change in the axial distance.
  • a change of at least .3 inches amounts to a 60%> change in the axial distance. It should be appreciated, however, that interpreting nominal changes in the axial distance in terms of a percent of a typical axial distance provides merely one example of a convenient measure of nominal changes, and that the invention is not necessarily limited in this respect. Rather, as discussed above, in general a "more than nominal" change in the typical axial distance refers to a change of greater than .15 inches in the axial distance.
  • a "sufficiently stable" power supplied by (or energy received by) the secondary winding 106 refers to a variation in the peak electrical power provided to a load (or in the energy received by the secondary winding) of less than 50%.
  • the energy received by the secondary winding 106 does not decrease by more than 50% due to a change (in particular, an increase) of more than .15 inches in the axial distance 18.
  • the typical axial distance may be increased by significantly more than 60-10% of the typical axial distance (e.g.. up to 200%) without a corresponding decrease of more than 50%o in the power supplied by the secondary winding.
  • the primary winding 102 and the secondary winding 106 may be constructed and arranged such that sufficient power is provided by the secondary winding at a "typical" axial distance 18 in a range of from approximately .5 to 1 inch (approximately 13-26 mm).
  • the primary and secondary windings may be constructed and arranged such that the power is not significantly affected (e.g., varies by less than 50 %>) due to changes in the typical axial distance 18 of from .25 to 1 inch (as much as a 200%) change in the axial distance), thus giving rise to an effective axial operating range of up to approximately 2 inches (50 mm).
  • Fig. 10 is a diagram similar to that of Fig. 9. in which the secondary winding 106 has been laterally displaced by a lateral distance 22 from the z-axis 12. along the x 2 -axis 16.
  • the geometric center of the secondary winding 106 following the lateral displacement is indicated by the reference character 20b.
  • the "former " ' geometric center of the secondary winding 106 prior to the lateral displacement is indicated by the reference character 20a.
  • the primary winding 102 and the secondary winding 106 of the TET device 100 are constructed and arranged such that the energy received by the secondary winding 106 is not significantly affected by a more than nominal lateral displacement between the primary and secondary windings, as indicated by the distance 22, at a typical axial distance 18. While in Fig. 10 only the secondary winding 106 is shown as having changed position from the arrangement shown in Fig. 9. it should be appreciated that the position of one or both of the primary winding 102 O 01/37926
  • the secondary winding 106 may be changed in either direction along the x-axis 14 and the x 2 -axis 16, respectively, as well as in either direction parallel to the y-axis 13. to create a lateral displacement between the two windings co ⁇ esponding to the lateral distance 22.
  • an oversized primary winding 102 as shown in Figs. 9 and 10 insures that the energy received by the secondary winding 106 is not significantly affected by a more than nominal lateral displacement between the primary and secondary windings 102 and 106.
  • an electrical power supplied by the secondary winding 106. based on the energy in the portion of the magnetic field received by the secondary winding, remains sufficiently stable notwithstanding a lateral displacement corresponding to the lateral distance 22. such that satisfactory operation of a device receiving power from the secondary winding 106 (e.g., the implanted device 1 10 shown in Fig. 1) is maintained.
  • a nominal lateral displacement refers to minor lateral displacements between the respective geometric centers of the areas delimited by the windings amounting to less than approximately .25 inches (approximately 13 mm). Accordingly, “more than nominal" lateral displacements refer to lateral displacements amounting to more than approximately .25 inches.
  • the secondary winding 106 intercepts an essentially constant or uniform magnetic flux from the primary winding 102.
  • This situation may be viewed conceptually by imagining the secondary winding 106 freely moving anywhere in its x-y plane within the confines of the cylindrical profile of magnetic flux lines 30 generated by the primary winding 102.
  • the power supplied by the secondary winding 106 to a device remains essentially constant.
  • the primary and secondary windings of the TET device 100 shown in Figs. 9 and 10 may be constructed and a ⁇ anged such that the energy received by the secondary winding 106 remains essentially constant, notwithstanding lateral displacements constituting a lateral distance 22 of between .5 and 2 inches (12-50 mm).
  • the maximum lateral displacement range in which constant received energy may be maintained is given by the distance 25, and hence is a function of the respective radii 202 and 204 of the windings 102 and 106.
  • - 19 - windings of the TET device 100 shown in Figs. 9 and 10 may be constructed and arranged such that for a maximum expected lateral displacement (which in some cases may exceed the distance 25 indicated in Fig. 9) the secondary winding 106 nonetheless intercepts a sufficient magnetic field so as to supply no less than 50%> of its full power capability (e.g., when the primary and secondary windings are "optimally" aligned, as shown in Fig. 9) to a device constituting a load on the secondary winding.
  • a magnetic field generated by the current . flowing through the primary winding 102 may be approximated as a cylindrical profile of magnetic flux lines 30 emanating from the plane of the primary winding 102.
  • the density B (in Webers/m 2 ) of the magnetic field represented by the cylinder of magnetic flux lines 30 may be given approximately by the expression
  • ⁇ is the "permeability" of the material through which the magnetic field passes (e.g.. skin, etc.)
  • N/ is the number of winding turns in the primary winding 102. is the current in the primary winding 102.
  • Ri is the radius 202 of the primary winding 102. Due to the smaller area delimited by the secondary winding 106. the secondary winding intercepts only some of the magnetic flux lines 30 and, hence, only a portion of the magnetic field generated by the primary winding 102.
  • a magnetic flux ⁇ 2 ⁇ (in Webers) intercepted by the secondary winding 106 due to a magnetic field generated by the primary winding may be expressed in terms of the density B of the magnetic field multiplied by the area 106' delimited by the secondary winding 106, as
  • a 2 is the area 106' delimited by the secondary winding 106
  • R ? is the radius 204 of the secondary winding 106.
  • a time-varying or alternating cu ⁇ ent i(t) in the primary winding 102 in turn generates a time-varying magnetic field which results in a time-varying flux ⁇ 2 ⁇ (t) intercepted by the secondary winding 106.
  • a time-varying flux induces a voltage v(.) across the secondary winding 106 according to Faraday's law, given as
  • N 2 is the number of winding turns in the secondary winding.
  • the voltage v(t) induced across the secondary winding 106 provides a source of electrical power to a load connected to the secondary winding.
  • the stability of the voltage in the secondary winding 106 depends upon the stability of the magnetic flux ⁇ > . ⁇ (t) intercepted by the secondary winding 106.
  • the larger size of the primary winding 102 with respect to the secondary winding 106 provides a cylindrical profile of magnetic flux lines, within which the secondary winding may move while nonetheless intercepting a stable magnetic flux ⁇ __,_(t) having an essentially constant amplitude.
  • the flux intercepted by the secondary winding 106 begins to decrease (the amplitude of the time-varying flux in Eq. (5) begins to decrease).
  • the voltage across the secondary winding according to Eq. (5) begins to decrease. resulting in a corresponding decrease in power supplied by the secondary winding 106 to a load.
  • the TET device 100 shown in Figs. 1 , 2, 3, 9, and 10 may provide several advantages particularly to prosthetic implant patients, as well as in a variety of other applications. Unlike conventional TET devices in which a primary winding is constrained to be located as close to the skin as possible, the TET device 100 has an increased effective operating range and permits an appreciable displacement between the primary and secondary windings, thereby affording greater flexibility and a greater freedom of movement for the patient.
  • the primary winding 102 of the TET device 100 may be attached, for example, to an article of clothing or placed in a pocket without adversely affecting the power supplied to an implanted device.
  • various medicated ointments, protective creams or cushions, bandages, and the like may be placed between the primary winding 102 and the patient ' s skin 302 to prevent and/or treat discomfort or irritation to the skin without adversely affecting the power supplied to an implanted device.
  • appropriate parameters e.g., the relative winding sizes, the number of winding turns for primary and secondary windings
  • the power requirements of one or more devices to receive power from the secondary winding, and the amount of displacement which is likely to occur between the primary and secondary windings during normal use are taken into consideration.
  • the primary and secondary windings are to be rigidly attached to a boundary of a system (e.g., the skin of the body) and maintained in predetermined positions, the amount of displacement which is likely to occur between the windings is low.
  • the respective areas delimited by the primary and secondary windings may be selected such that the ratio of the areas is closer to two, thereby increasing the magnetic coupling and hence the energy transfer efficiency of the TET device.
  • the primary and/or secondary winding may not be so rigidly attached to a boundary (e.g.. the primary winding may be attached to an article of clothing).
  • the respective areas delimited by the primary and secondary windings may be selected such that the ratio of the areas is sufficient to allow for greater displacement without variation in the power supplied by the secondary winding.
  • the primary winding may have a diameter 24 of between 3 and 6 inches (75-150 mm) and the secondary winding 102 may have a diameter 26 of between 1 and 3 inches (25-75 mm).
  • a primary winding larger than 6 inches may become too bulky and uncomfortable to wear for a patient, while a primary winding smaller than 3 inches may provide too small of an effective operating range.
  • a secondary winding larger than 3 inches may be excessively large to implant in a patient, while a secondary winding smaller than 1 inch may not provide sufficient power to a device, as discussed further below.
  • a smaller secondary winding is capable of transferring less power to a device than would a larger secondary winding, based on an equivalent energy received by the secondary winding.
  • an appropriate number of winding turns for the respective primary and secondary windings may be selected based on an anticipated size (area) of the windings, power requirements of the load, and voltage and cu ⁇ ent operating conditions of both the external power supply supplying power to the primary winding and the load.
  • the primary and secondary windings may be configured as "tuned" circuits, wherein the energy is transfe ⁇ ed between the primary and secondary windings at or near a particular resonant frequency that is amplified by the secondary tuned circuit, to compensate for a lower energy transfer efficiency of the TET device due to an oversized primary winding.
  • Fig. 11 is a "side" view similar to that of Fig.
  • Fig. 1 1 shows the primary winding 102 and the secondary winding 106 in greater detail.
  • the primary winding 102 may include from 3 to 5 winding turns 402 in an essentially planar configuration
  • the secondary winding 106 may include from 12 to 16 winding turns 404 a ⁇ anged in multiple layers as a "squashed helix.”
  • design parameters of the primary and secondary windings shown in Fig. 1 1 may be determined somewhat empirically using basic transformer operating principles, based on the geometry and operating conditions of the TET device. For example, first a target resonant frequency may be selected to transfer energy from the primary winding 102 to the secondary winding 106. The target resonant frequency may be based on an approximate area delimited by the secondary winding which is suitable for human use, and a suitably small capacitor (not shown in Fig. 11) for the resonant
  • a secondary winding delimiting an area 106' of approximately 5 square inches can accommodate a capacitor having a capacitance as low as approximately 10 nanofarads (nF).
  • the capacitance of the capacitor for the secondary winding tuned circuit is preferably as low as possible given the available volume for the capacitor to occupy, so that RF losses are sufficiently low.
  • a target inductance for the secondary winding 106 can be determined. For example, in one embodiment, a target resonant frequency of approximately 300 kHz and a capacitance of 10 nF results in a target secondary winding inductance of approximately 30 ⁇ H. Such a target inductance may be achieved in a secondary winding delimiting an approximately circular area having a diameter of approximately 2.5 inches using approximately 14 winding turns 404. It should be appreciated that according to other embodiments involving different secondary winding geometries and sizes, the number of winding turns 404 required to achieve the target inductance varies accordingly.
  • the number of primary winding turns 402 may be determined based in part on the voltage requirements of the load and the output voltage of the external power supply that provides power to the primary winding.
  • a "turns ratio" between the primary and secondary windings determines in part a co ⁇ esponding voltage ratio between a voltage across the primary winding and a voltage across the secondary winding.
  • the external power supply has an operating voltage in a range of from 15-30 volts
  • the load on the secondary winding similarly has an operating voltage in a range of from 15-30 volts.
  • a high turns ratio secondary winding to primary winding is desirable in this aspect to achieve a high voltage transfer ratio so as to compensate in part for the low energy transfer efficiency.
  • an oversized primary winding delimiting an approximately circular area 102' having a diameter of approximately 5.5 inches is constructed to have approximately 4 winding turns 402.
  • the resulting inductance of such a primary winding is approximately 3 ⁇ H.
  • the number of primary winding turns 402 may be determined empirically from an iteraxive process until a desired secondary winding voltage is achieved.
  • the primary tuned circuit capacitance is chosen such that the primary resonant frequency and the secondary resonant frequency are approximately equal. Accordingly, based on a primary winding inductance of 3 ⁇ H, a primary (and secondary) resonant frequency of 300 kHz in the present example co ⁇ esponds to a primary capacitance of approximately 100 nF.
  • a power output of 15 to 50 watts at a voltage of 15 to 30 volts and a cu ⁇ ent of 2 to 3 amps may be supplied by the secondary winding 106 to one or more devices such as the implanted device 110 shown in Fig. 1 over the effective operating range of the TET device 100.
  • a TET device having parameters similar to those outlined above accordingly is capable of an energy transfer efficiency (power output/power input) of as high as 75-80%).

Landscapes

  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Radiology & Medical Imaging (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Prostheses (AREA)

Abstract

L'invention concerne des procédés et un appareil pour le transfert de l'énergie au-delà d'une limite, de sorte que de l'énergie soit fournie à des dispositifs (110) se trouvant à l'intérieur du corps. Ledit appareil comprend : un dispositif de transfert d'énergie transcutané TET (100) fonctionnant comme un transformateur de puissance comprenant un enroulement primaire surdimensionné (102) fixé à proximité d'une surface extérieure de la peau, et un enroulement secondaire (106) implanté dans le corps et aligné avec l'enroulement primaire. Une première zone délimitée par l'enroulement primaire, de laquelle un champ magnétique est généré, est d'une taille supérieure à une deuxième zone délimitée par l'enroulement secondaire du transformateur TET qui intercepte le champ magnétique. La zone la plus grande de l'enroulement primaire surdimensionné permet un déplacement sensible entre les enroulements primaire et secondaire et le maintien de l'homogénéité du champ magnétique heurtant l'enroulement secondaire. Ainsi, l'enroulement secondaire peut fournir suffisamment d'énergie à un ou plusieurs dispositifs implantés, quels que soient les écarts entre les positions relatives des enroulements.
PCT/US2000/031923 1999-11-22 2000-11-21 Appareil pour le transfert d'energie au-dela d'une limite WO2001037926A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
EP00978846A EP1231981A1 (fr) 1999-11-22 2000-11-21 Appareil pour le transfert d'energie au-dela d'une limite

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US44459199A 1999-11-22 1999-11-22
US09/444,591 1999-11-22

Publications (1)

Publication Number Publication Date
WO2001037926A1 true WO2001037926A1 (fr) 2001-05-31

Family

ID=23765544

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US2000/031923 WO2001037926A1 (fr) 1999-11-22 2000-11-21 Appareil pour le transfert d'energie au-dela d'une limite

Country Status (2)

Country Link
EP (1) EP1231981A1 (fr)
WO (1) WO2001037926A1 (fr)

Cited By (38)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2004028623A1 (fr) * 2002-09-25 2004-04-08 Potencia Medical Ag Detection d'un dispositif de reception d'energie sans fil implante
US6773429B2 (en) 2000-10-11 2004-08-10 Microchips, Inc. Microchip reservoir devices and facilitated corrosion of electrodes
US6976982B2 (en) 2001-01-09 2005-12-20 Microchips, Inc. Flexible microchip devices for ophthalmic and other applications
US7226442B2 (en) 2000-10-10 2007-06-05 Microchips, Inc. Microchip reservoir devices using wireless transmission of power and data
US7599737B2 (en) 2002-10-04 2009-10-06 Microchips, Inc. Medical device for neural stimulation and controlled drug delivery
US7650187B2 (en) 2003-11-18 2010-01-19 DEUTSCHES ZENTRUM FüR LUFT-UND RAUMFAHRT E.V. Assembly for wireless energy communication to an implanted device
WO2010059097A1 (fr) * 2008-11-21 2010-05-27 Milux Holding S.A. Système, procédé et appareil de fourniture d'énergie à un dispositif médical implantable
WO2010059096A1 (fr) * 2008-11-21 2010-05-27 Milux Holding S.A. Système de fourniture d’énergie
US7780613B2 (en) 2005-06-30 2010-08-24 Depuy Products, Inc. Apparatus, system, and method for transcutaneously transferring energy
US7917208B2 (en) 2002-10-04 2011-03-29 Microchips, Inc. Medical device for controlled drug delivery and cardiac monitoring and/or stimulation
US8015024B2 (en) 2006-04-07 2011-09-06 Depuy Products, Inc. System and method for managing patient-related data
US8075627B2 (en) 2006-04-07 2011-12-13 Depuy Products, Inc. System and method for transmitting orthopaedic implant data
US8080064B2 (en) 2007-06-29 2011-12-20 Depuy Products, Inc. Tibial tray assembly having a wireless communication device
US8403915B2 (en) 2004-09-01 2013-03-26 Microchips, Inc. Multi-opening reservoir devices for controlled release or exposure of reservoir contents
US8632464B2 (en) 2006-09-11 2014-01-21 DePuy Synthes Products, LLC System and method for monitoring orthopaedic implant data
WO2014018964A2 (fr) 2012-07-27 2014-01-30 Thoratec Corporation Gestion thermique pour des systèmes de transfert de puissance sans fil implantables
WO2014018973A1 (fr) 2012-07-27 2014-01-30 Thoratec Corporation Bobines et systèmes de transmission de puissance résonants
WO2014145895A1 (fr) 2013-03-15 2014-09-18 Thoratec Corporation Bobine de système de transfert d'énergie transcutané (tets) malléable à ajustement anatomique amélioré
WO2015070200A1 (fr) 2013-11-11 2015-05-14 Thoratec Corporation Systèmes de transfert de puissance par résonance avec communications
US9287040B2 (en) 2012-07-27 2016-03-15 Thoratec Corporation Self-tuning resonant power transfer systems
WO2016049039A1 (fr) 2014-09-22 2016-03-31 Thoratec Corporation Conceptions d'antenne pour communication entre un implant alimenté sans fil et un dispositif externe à l'extérieur du corps
US9583874B2 (en) 2014-10-06 2017-02-28 Thoratec Corporation Multiaxial connector for implantable devices
WO2017062552A1 (fr) 2015-10-07 2017-04-13 Tc1 Llc Systèmes de transfert d'énergie par résonance à optimisation du rendement basée sur l'impédance du récepteur
US9680310B2 (en) 2013-03-15 2017-06-13 Thoratec Corporation Integrated implantable TETS housing including fins and coil loops
US9780596B2 (en) 2013-07-29 2017-10-03 Alfred E. Mann Foundation For Scientific Research Microprocessor controlled class E driver
US9805863B2 (en) 2012-07-27 2017-10-31 Thoratec Corporation Magnetic power transmission utilizing phased transmitter coil arrays and phased receiver coil arrays
US9825471B2 (en) 2012-07-27 2017-11-21 Thoratec Corporation Resonant power transfer systems with protective algorithm
US9855437B2 (en) 2013-11-11 2018-01-02 Tc1 Llc Hinged resonant power transfer coil
US9855436B2 (en) 2013-07-29 2018-01-02 Alfred E. Mann Foundation For Scientific Research High efficiency magnetic link for implantable devices
WO2018057563A1 (fr) 2016-09-21 2018-03-29 Tc1 Llc Systèmes et procédés de localisation de dispositifs de transmission de puissance sans fil implantés
US10148126B2 (en) 2015-08-31 2018-12-04 Tc1 Llc Wireless energy transfer system and wearables
US10291067B2 (en) 2012-07-27 2019-05-14 Tc1 Llc Computer modeling for resonant power transfer systems
WO2019135890A1 (fr) 2018-01-04 2019-07-11 Tc1 Llc Systèmes et procédés de dispositifs de transmission d'énergie sans fil élastique
US10525181B2 (en) 2012-07-27 2020-01-07 Tc1 Llc Resonant power transfer system and method of estimating system state
US10615642B2 (en) 2013-11-11 2020-04-07 Tc1 Llc Resonant power transfer systems with communications
US10610692B2 (en) 2014-03-06 2020-04-07 Tc1 Llc Electrical connectors for implantable devices
US11197990B2 (en) 2017-01-18 2021-12-14 Tc1 Llc Systems and methods for transcutaneous power transfer using microneedles
US11642537B2 (en) 2019-03-11 2023-05-09 Axonics, Inc. Charging device with off-center coil

Families Citing this family (6)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP7414529B2 (ja) 2017-06-07 2024-01-16 シファメド・ホールディングス・エルエルシー 血管内流体移動デバイス、システム、および使用方法
WO2019094963A1 (fr) 2017-11-13 2019-05-16 Shifamed Holdings, Llc Dispositifs de déplacement de liquide intravasculaire, systèmes et procédés d'utilisation
WO2019152875A1 (fr) 2018-02-01 2019-08-08 Shifamed Holdings, Llc Pompes à sang intravasculaires et méthodes d'utilisation et procédés de fabrication
US11964145B2 (en) 2019-07-12 2024-04-23 Shifamed Holdings, Llc Intravascular blood pumps and methods of manufacture and use
US11654275B2 (en) 2019-07-22 2023-05-23 Shifamed Holdings, Llc Intravascular blood pumps with struts and methods of use and manufacture
EP4034192A4 (fr) 2019-09-25 2023-11-29 Shifamed Holdings, LLC Dispositifs et systèmes de pompes à sang intravasculaires et leurs procédés d'utilisation et de commande

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE3736170A1 (de) * 1987-10-26 1989-05-18 Mesa Systemtechnik Ges Fuer Me Vorrichtung zum beruehrungslosen uebertragen einer leistung unter einsatz von elektrizitaet
US5405367A (en) * 1991-12-18 1995-04-11 Alfred E. Mann Foundation For Scientific Research Structure and method of manufacture of an implantable microstimulator
US5703461A (en) * 1995-06-28 1997-12-30 Kabushiki Kaisha Toyoda Jidoshokki Seisakusho Inductive coupler for electric vehicle charger
US5741316A (en) * 1996-12-02 1998-04-21 Light Sciences Limited Partnership Electromagnetic coil configurations for power transmission through tissue

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE3736170A1 (de) * 1987-10-26 1989-05-18 Mesa Systemtechnik Ges Fuer Me Vorrichtung zum beruehrungslosen uebertragen einer leistung unter einsatz von elektrizitaet
US5405367A (en) * 1991-12-18 1995-04-11 Alfred E. Mann Foundation For Scientific Research Structure and method of manufacture of an implantable microstimulator
US5703461A (en) * 1995-06-28 1997-12-30 Kabushiki Kaisha Toyoda Jidoshokki Seisakusho Inductive coupler for electric vehicle charger
US5741316A (en) * 1996-12-02 1998-04-21 Light Sciences Limited Partnership Electromagnetic coil configurations for power transmission through tissue

Cited By (78)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7226442B2 (en) 2000-10-10 2007-06-05 Microchips, Inc. Microchip reservoir devices using wireless transmission of power and data
US6773429B2 (en) 2000-10-11 2004-08-10 Microchips, Inc. Microchip reservoir devices and facilitated corrosion of electrodes
US6976982B2 (en) 2001-01-09 2005-12-20 Microchips, Inc. Flexible microchip devices for ophthalmic and other applications
US7776024B2 (en) 2001-01-09 2010-08-17 Microchips, Inc. Method of actuating implanted medical device
US7879019B2 (en) 2001-01-09 2011-02-01 Microchips, Inc. Method of opening reservoir of containment device
WO2004028623A1 (fr) * 2002-09-25 2004-04-08 Potencia Medical Ag Detection d'un dispositif de reception d'energie sans fil implante
US7917208B2 (en) 2002-10-04 2011-03-29 Microchips, Inc. Medical device for controlled drug delivery and cardiac monitoring and/or stimulation
US7599737B2 (en) 2002-10-04 2009-10-06 Microchips, Inc. Medical device for neural stimulation and controlled drug delivery
US7650187B2 (en) 2003-11-18 2010-01-19 DEUTSCHES ZENTRUM FüR LUFT-UND RAUMFAHRT E.V. Assembly for wireless energy communication to an implanted device
DE10353943B4 (de) * 2003-11-18 2013-01-03 Deutsches Zentrum für Luft- und Raumfahrt e.V. Anordnung zur drahtlosen Energieübertragung an eine implantierte Einrichtung
US8403915B2 (en) 2004-09-01 2013-03-26 Microchips, Inc. Multi-opening reservoir devices for controlled release or exposure of reservoir contents
US7780613B2 (en) 2005-06-30 2010-08-24 Depuy Products, Inc. Apparatus, system, and method for transcutaneously transferring energy
US8015024B2 (en) 2006-04-07 2011-09-06 Depuy Products, Inc. System and method for managing patient-related data
US8075627B2 (en) 2006-04-07 2011-12-13 Depuy Products, Inc. System and method for transmitting orthopaedic implant data
US10172551B2 (en) 2006-04-07 2019-01-08 DePuy Synthes Products, Inc. System and method for transmitting orthopaedic implant data
US8668742B2 (en) 2006-04-07 2014-03-11 DePuy Synthes Products, LLC System and method for transmitting orthopaedic implant data
US8632464B2 (en) 2006-09-11 2014-01-21 DePuy Synthes Products, LLC System and method for monitoring orthopaedic implant data
US8080064B2 (en) 2007-06-29 2011-12-20 Depuy Products, Inc. Tibial tray assembly having a wireless communication device
EP2385805A1 (fr) * 2008-11-21 2011-11-16 Milux Holding SA Système de fourniture d'énergie
US20110278948A1 (en) * 2008-11-21 2011-11-17 Milux Holdings SA System for supplying energy
EP2385805A4 (fr) * 2008-11-21 2012-10-17 Milux Holding Sa Système de fourniture d'énergie
WO2010059096A1 (fr) * 2008-11-21 2010-05-27 Milux Holding S.A. Système de fourniture d’énergie
WO2010059097A1 (fr) * 2008-11-21 2010-05-27 Milux Holding S.A. Système, procédé et appareil de fourniture d'énergie à un dispositif médical implantable
US8862241B2 (en) 2008-11-21 2014-10-14 Peter Forsell System for supplying energy to an implantable medical device
EP4257174A2 (fr) 2012-07-27 2023-10-11 Tc1 Llc Gestion thermique pour systèmes de transfert d'énergie sans fil implantables
US10637303B2 (en) 2012-07-27 2020-04-28 Tc1 Llc Magnetic power transmission utilizing phased transmitter coil arrays and phased receiver coil arrays
US10693299B2 (en) 2012-07-27 2020-06-23 Tc1 Llc Self-tuning resonant power transfer systems
US9287040B2 (en) 2012-07-27 2016-03-15 Thoratec Corporation Self-tuning resonant power transfer systems
US10668197B2 (en) 2012-07-27 2020-06-02 Tc1 Llc Resonant power transmission coils and systems
WO2014018964A2 (fr) 2012-07-27 2014-01-30 Thoratec Corporation Gestion thermique pour des systèmes de transfert de puissance sans fil implantables
US9592397B2 (en) 2012-07-27 2017-03-14 Thoratec Corporation Thermal management for implantable wireless power transfer systems
WO2014018973A1 (fr) 2012-07-27 2014-01-30 Thoratec Corporation Bobines et systèmes de transmission de puissance résonants
US10525181B2 (en) 2012-07-27 2020-01-07 Tc1 Llc Resonant power transfer system and method of estimating system state
US10434235B2 (en) 2012-07-27 2019-10-08 Tci Llc Thermal management for implantable wireless power transfer systems
US9805863B2 (en) 2012-07-27 2017-10-31 Thoratec Corporation Magnetic power transmission utilizing phased transmitter coil arrays and phased receiver coil arrays
US9825471B2 (en) 2012-07-27 2017-11-21 Thoratec Corporation Resonant power transfer systems with protective algorithm
US10291067B2 (en) 2012-07-27 2019-05-14 Tc1 Llc Computer modeling for resonant power transfer systems
US10251987B2 (en) 2012-07-27 2019-04-09 Tc1 Llc Resonant power transmission coils and systems
US9997928B2 (en) 2012-07-27 2018-06-12 Tc1 Llc Self-tuning resonant power transfer systems
US10636566B2 (en) 2013-03-15 2020-04-28 Tc1 Llc Malleable TETS coil with improved anatomical fit
EP3490102A1 (fr) 2013-03-15 2019-05-29 Thoratec Corporation Bobine tets malléable présentant un meilleur ajustement anatomique
WO2014145895A1 (fr) 2013-03-15 2014-09-18 Thoratec Corporation Bobine de système de transfert d'énergie transcutané (tets) malléable à ajustement anatomique amélioré
US9680310B2 (en) 2013-03-15 2017-06-13 Thoratec Corporation Integrated implantable TETS housing including fins and coil loops
US10476317B2 (en) 2013-03-15 2019-11-12 Tci Llc Integrated implantable TETs housing including fins and coil loops
US10373756B2 (en) 2013-03-15 2019-08-06 Tc1 Llc Malleable TETs coil with improved anatomical fit
US10971950B2 (en) 2013-07-29 2021-04-06 The Alfred E. Mann Foundation For Scientific Research Microprocessor controlled class E driver
US9855436B2 (en) 2013-07-29 2018-01-02 Alfred E. Mann Foundation For Scientific Research High efficiency magnetic link for implantable devices
US9780596B2 (en) 2013-07-29 2017-10-03 Alfred E. Mann Foundation For Scientific Research Microprocessor controlled class E driver
US10447083B2 (en) 2013-07-29 2019-10-15 The Alfred E. Mann Foundation For Scientific Research Microprocessor controlled class E driver
US10449377B2 (en) 2013-07-29 2019-10-22 The Alfred E. Mann Foundation For Scientific Research High efficiency magnetic link for implantable devices
US11722007B2 (en) 2013-07-29 2023-08-08 The Alfred E. Mann Foundation For Scientific Rsrch Microprocessor controlled class E driver
WO2015070200A1 (fr) 2013-11-11 2015-05-14 Thoratec Corporation Systèmes de transfert de puissance par résonance avec communications
US9855437B2 (en) 2013-11-11 2018-01-02 Tc1 Llc Hinged resonant power transfer coil
US10873220B2 (en) 2013-11-11 2020-12-22 Tc1 Llc Resonant power transfer systems with communications
US10695476B2 (en) 2013-11-11 2020-06-30 Tc1 Llc Resonant power transfer systems with communications
US10615642B2 (en) 2013-11-11 2020-04-07 Tc1 Llc Resonant power transfer systems with communications
US10610692B2 (en) 2014-03-06 2020-04-07 Tc1 Llc Electrical connectors for implantable devices
US10186760B2 (en) 2014-09-22 2019-01-22 Tc1 Llc Antenna designs for communication between a wirelessly powered implant to an external device outside the body
EP4213298A1 (fr) 2014-09-22 2023-07-19 Tc1 Llc Conceptions d'antenne pour communication entre un implant alimenté sans fil et un dispositif externe à l'extérieur du corps
WO2016049039A1 (fr) 2014-09-22 2016-03-31 Thoratec Corporation Conceptions d'antenne pour communication entre un implant alimenté sans fil et un dispositif externe à l'extérieur du corps
US11245181B2 (en) 2014-09-22 2022-02-08 Tc1 Llc Antenna designs for communication between a wirelessly powered implant to an external device outside the body
EP3826104A1 (fr) 2014-09-22 2021-05-26 Tc1 Llc Conceptions d'antenne de communication entre un implant à alimentation sans fil et un dispositif externe à l'extérieur du corps
US10265450B2 (en) 2014-10-06 2019-04-23 Tc1 Llc Multiaxial connector for implantable devices
US9583874B2 (en) 2014-10-06 2017-02-28 Thoratec Corporation Multiaxial connector for implantable devices
US10770919B2 (en) 2015-08-31 2020-09-08 Tc1 Llc Wireless energy transfer system and wearables
US10148126B2 (en) 2015-08-31 2018-12-04 Tc1 Llc Wireless energy transfer system and wearables
US10804744B2 (en) 2015-10-07 2020-10-13 Tc1 Llc Resonant power transfer systems having efficiency optimization based on receiver impedance
US10177604B2 (en) 2015-10-07 2019-01-08 Tc1 Llc Resonant power transfer systems having efficiency optimization based on receiver impedance
EP3902100A1 (fr) 2015-10-07 2021-10-27 Tc1 Llc Systèmes de transfert d'énergie par résonance à optimisation du rendement basée sur l'impédance du récepteur
WO2017062552A1 (fr) 2015-10-07 2017-04-13 Tc1 Llc Systèmes de transfert d'énergie par résonance à optimisation du rendement basée sur l'impédance du récepteur
WO2018057563A1 (fr) 2016-09-21 2018-03-29 Tc1 Llc Systèmes et procédés de localisation de dispositifs de transmission de puissance sans fil implantés
US10898292B2 (en) 2016-09-21 2021-01-26 Tc1 Llc Systems and methods for locating implanted wireless power transmission devices
US11317988B2 (en) 2016-09-21 2022-05-03 Tc1 Llc Systems and methods for locating implanted wireless power transmission devices
EP4084271A1 (fr) 2016-09-21 2022-11-02 Tc1 Llc Systèmes et procédés de localisation de dispositifs implantés de transmission de puissance sans fil
US11197990B2 (en) 2017-01-18 2021-12-14 Tc1 Llc Systems and methods for transcutaneous power transfer using microneedles
US10770923B2 (en) 2018-01-04 2020-09-08 Tc1 Llc Systems and methods for elastic wireless power transmission devices
WO2019135890A1 (fr) 2018-01-04 2019-07-11 Tc1 Llc Systèmes et procédés de dispositifs de transmission d'énergie sans fil élastique
US11642537B2 (en) 2019-03-11 2023-05-09 Axonics, Inc. Charging device with off-center coil

Also Published As

Publication number Publication date
EP1231981A1 (fr) 2002-08-21

Similar Documents

Publication Publication Date Title
WO2001037926A1 (fr) Appareil pour le transfert d'energie au-dela d'une limite
US7599744B2 (en) Transcutaneous energy transfer primary coil with a high aspect ferrite core
KR100606307B1 (ko) 인체 이식 기구용 무접촉식 동력 전달 장치
RU2440832C2 (ru) Низкочастотный чрескожный перенос энергии на имплантированное медицинское устройство
US5991664A (en) Compact inductive arrangement for medical implant data and power transfer
US7191007B2 (en) Spatially decoupled twin secondary coils for optimizing transcutaneous energy transfer (TET) power transfer characteristics
US7209792B1 (en) RF-energy modulation system through dynamic coil detuning
AU2003263710B2 (en) Harmless wireless energy transmission to implant
US20020087204A1 (en) Flexible transcutaneous energy transfer (TET) primary coil
US8845510B2 (en) Flexible galvanic primary and non galvanic secondary coils for wireless coplanar energy transfer (CET)
AU2013203810A1 (en) Methods, systems, and devices relating to wireless power transfer
WO2001074447A3 (fr) Appareil a bobine d'induction pour telemetrie biomedicale
US20140114373A1 (en) Intermediate Coupler to Facilitate Charging in an Implantable Medical Device System
Campi et al. Feasibility study of a wireless power transfer system applied to a left ventricular assist device
AU2011253672B2 (en) Transcutaneous energy transfer primary coil with a high aspect ferrite core
Aubakirov et al. Operating Frequency Effect on LC-circuit Flat Circular Coils in Inductive Powering Unit for Implants
AU711002B2 (en) Compact inductive arrangement

Legal Events

Date Code Title Description
AK Designated states

Kind code of ref document: A1

Designated state(s): CA JP

AL Designated countries for regional patents

Kind code of ref document: A1

Designated state(s): AT BE CH CY DE DK ES FI FR GB GR IE IT LU MC NL PT SE TR

121 Ep: the epo has been informed by wipo that ep was designated in this application
DFPE Request for preliminary examination filed prior to expiration of 19th month from priority date (pct application filed before 20040101)
WWE Wipo information: entry into national phase

Ref document number: 2000978846

Country of ref document: EP

WWP Wipo information: published in national office

Ref document number: 2000978846

Country of ref document: EP

WWW Wipo information: withdrawn in national office

Ref document number: 2000978846

Country of ref document: EP