WO2017025606A1 - Système, appareil et procédé de transfert de courant sans contact amélioré dans des dispositifs implantables - Google Patents

Système, appareil et procédé de transfert de courant sans contact amélioré dans des dispositifs implantables Download PDF

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Publication number
WO2017025606A1
WO2017025606A1 PCT/EP2016/069159 EP2016069159W WO2017025606A1 WO 2017025606 A1 WO2017025606 A1 WO 2017025606A1 EP 2016069159 W EP2016069159 W EP 2016069159W WO 2017025606 A1 WO2017025606 A1 WO 2017025606A1
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WO
WIPO (PCT)
Prior art keywords
power
implantable
power supply
rechargeable
coil
Prior art date
Application number
PCT/EP2016/069159
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English (en)
Inventor
Vegard Tuseth
Eric Rudie
Shawn Patterson
Stanley KLUGE
Matthew KEILLOR
Original Assignee
Nuheart As
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
Priority claimed from US14/825,054 external-priority patent/US20170043077A1/en
Priority claimed from US14/825,022 external-priority patent/US20170047762A1/en
Priority claimed from US14/923,256 external-priority patent/US20170117739A1/en
Application filed by Nuheart As filed Critical Nuheart As
Publication of WO2017025606A1 publication Critical patent/WO2017025606A1/fr

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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 generally belongs to the field of contactless power transfer for medical devices. More specifically, the present invention relates to contactless power transfer for intra-corporeal medical devices.
  • the present invention is particularly useful in the context of minimally invasive procedures, for example those described in PCT application No. PCT/EP2015/055578, entitled 'PERCUTANEOUS SYSTEM, DEVICES AND METHODS,' filed 17 March 2015 and expressly incorporated herein by reference in its entirety.
  • Examples of medical devices that may be suitable for contactless power transfer include implantable medical devices and mechanical circulatory support systems (MCS), for example ventricular assist devices (VADs).
  • a VAD is a mechanical pumping device capable of supporting heart function and blood flow. Specifically, a VAD helps one or both ventricles of the heart to pump blood through the circulatory system.
  • Left ventricular assist devices (LVAD), right ventricular assist devices (RVAD) and biventricular assist devices (BiVAD) are currently available.
  • Circulatory support systems may also include cardiopulmonary support (CPS, ECMO), which provide means for blood oxygenation as well as blood pumping.
  • CPS cardiopulmonary support
  • ECMO cardiopulmonary support
  • Such devices may be required during, before and/or after heart surgery or to treat severe heart conditions such as heart failure, cardiopulmonary arrest (CPA), ventricular arrhythmia or cardiogenic shock.
  • an implanted device affects the comfort of a patient.
  • a large or bulky implanted device will require more complex surgery and a longer recovery time compared to a small implanted device.
  • An example of such a device is an implantable pacemaker.
  • a pacemaker requires surgery in order to be implant a battery subcutaneously within a patient's body. Such surgical procedures are clearly invasive and unsuitable for weaker and vulnerable patients as they involve a greater recovery time and carry risks of infection and trauma.
  • Transcatheter implantation of VADs involves the insertion through a small incision or puncture made at the groin area of a patient.
  • Existing procedures involve a catheter introduced through an incision adjacent to the groin of the patient and advanced along the femoral vein and inferior vena cava, across the intra-atrial septum and into the left atrium.
  • punctures can be created by known methods using the catheter and the various devices can be inserted through and implanted via the same catheter.
  • a problem with these types of devices is the incorporation of the battery.
  • a battery can occupy around 50% to 80% of the volume of most implantable medical devices.
  • batteries have a limited lifespan requiring periodic interventions to replace or maintain the batteries.
  • transcutaneous power transmission non-contact type power transmission.
  • problems relating to miniaturisation of the devices and excess heat generation have been reported.
  • Past efforts using transcutaneous power transfer (magnetic induction) to recharge experimental implanted LVADs were unsuccessful due to the excessive heating of primary and secondary coils. Heating of a coil implanted subcutaneously in the body is undesirable as the surrounding tissue is not a good conductor of heat. This leads to localised heating and tissue damage surrounding the subcutaneous coil.
  • a rechargeable power supply for an intra-corporeal medical device comprising an implantable means for wirelessly receiving power and an implantable power storage means.
  • the rechargeable power supply according to the present invention reduces the need for a large implantable power storage means.
  • the power storage means can be wirelessly charged and, therefore, the size of the power storage means can be significantly reduced. This reduces the complexity of the surgery required to implant the power storage means and/or the medical device as the elements are substantially smaller.
  • the rechargeable power supply can be arranged and configured to be implanted within the circulatory system via, for example, percutaneous and/or transcatheter methods.
  • the rechargeable power supply is arranged and configured to be implanted within the intravascular and or cardiovascular system of a patient, for example a vein, artery or vena cava. Implantation utilising the intravascular system results in less traumatic procedures because fewer puncture/incision sites are required.
  • the rechargeable power supply and the intra-corporeal device to be charged may be implanted via a single puncture/incision site, and moved into position via the vascular system as a means of transportation, thereby by-passing internal anatomical walls.
  • the present invention is particularly advantageous when used in conjunction with transcatheter medical devices, as both the medical device and the power supply can be inserted through and positioned in the same anatomical space, e.g. in the cardiovascular system. Consequently, the risk of cross-contamination between anatomical spaces and infection is reduced.
  • anatomical space or “anatomical compartment” can be used interchangeably and may be the vascular system, the cardio vascular system, the gastric system, the respiratory system or other anatomical compartments.
  • percutaneous and transcatheter methods can be used interchangeably and refer to methods involving a procedure carried out through or via a tubing or catheter positioned in the patient's body.
  • intra-corporeal means inside the patient's body and "extra-corporeal” means outside the patient's body.
  • an advantage may be that the rechargeable power supply, which may consist of a coil and a battery, may not need to be recovered for maintenance purposes.
  • the battery can be charged whilst still implanted in the body and can remain for a semi-permanent basis, until for example the device is no longer required or a defect needs to be fixed.
  • the implantable power receiving means is arranged and configured to receive power from an extra-corporeal means for wirelessly transmitting power.
  • An advantage of this feature is that the implantable means of the rechargeable power supply can be charged without removal of these elements.
  • the implantable power receiving means further comprises implantable means for supplying the power received by the power receiving means to the power storage means.
  • implantable means for supplying the power received by the power receiving means to the power storage means.
  • the power can be configured prior to receipt by the power storage means, for example an AC-DC converter.
  • the implantable power receiving means is arranged and configured to receive power in the form of magnetic flux.
  • the magnetic flux can harmlessly propagate through the body of a patient, allowing for contactless power transfer.
  • the implantable power receiving means and an extra-corporeal means for wirelessly receiving power are positioned to enable magnetic coupling, thereby enabling power transmission between the extra-corporeal power transmitting means and the implantable power receiving means.
  • An advantage of this feature is that correct alignment increases coupling between the different means, allowing more efficient and quicker power transfer between the means. This may also reduce undesirable heating of the means during power transfer.
  • the implantable power receiving means comprises an electromagnetic coil.
  • the coil may be concentrically wound (i.e. a planar or flat coil) or be helical (i.e. a solenoid).
  • the coil may comprise a solenoid.
  • An advantage of a solenoid is that it can be implanted in the vascular system through a catheter, i.e. without requiring surgery.
  • a solenoid can be implanted in an area less exposed to impacts (for example in the cardiovascular system), thus reducing the chances of damage from impacts to the patient's body.
  • most planar coils are implanted subcutaneously, so that they can follow the shape of the patient's skin surface. However, subcutaneous coils are more exposed to impact and, in view of their shape, more likely to become deformed due to impact or even just physical movement. If the shape of the coil becomes distorted, then the efficiency of the power receiving means will become affected.
  • a power receiving means comprising a solenoid
  • the solenoid can dissipate heat more efficiently compared to a planar device. This is particularly true when the power receiving means is positioned where more of its surface area is in contact with bodily fluids. For example, when the power receiving means is positioned in the vascular system, the patient's blood can cool it down and there is no risk of overheating owing to the patient's blood flow which dissipates the heat. Thus a solenoid may not require a cooling system in order to operate safely and efficiently.
  • the electromagnetic coil is arranged around a former/bobbin made of an insulating material.
  • the former provides support for the electromagnetic coil. This prevents the coil from being crushed or becoming deformed in the presence of an impact. Furthermore, the former reduces mechanical vibrations in the coil, which reduces variations in the generated inductance.
  • the former comprises a magnetic material.
  • a magnetic material may be positioned within the former, wherein the former insulates the electromagnetic coil from the magnetic material. Using a magnetic material increases the inductance generated by the coil.
  • the power storage means of the rechargeable power supply comprises a magnetic material .
  • the power storage means is substantially cylindrical. This has an advantage of facilitating easier implantation due to the shape of the power storage means approximating the shape of the circulatory system.
  • the magnetic material of the power storage means extends along part of or along the whole of the longitudinal axis of the power storage means.
  • the magnetic material comprises iron and/or ferrite.
  • the longitudinal axis of the electromagnetic coil is arranged and configured to be substantially parallel to the longitudinal axis of an extra-corporeal power transmitting means, more preferably coaxial.
  • An advantage of this feature is that rotation of the electromagnetic coil around its longitudinal axis will not affect the coupling efficiency of the electromagnetic coil with respect to the extra-corporeal power transmitting means. This is particularly advantageous when the longitudinal axis of the coil is positioned vertically with respect to an anatomically vertical portion of a vein or artery, for example a portion of the vena cava.
  • the expression “vertical” is used relative to the human body, i.e. in the head-feet direction.
  • the rechargeable power supply comprises an extra-corporeal power transmitting means, which will be described in more detail below.
  • the implantable power receiving means and the extra-corporeal power transmitting means operate at substantially the same resonant frequency.
  • An advantage of this feature is that the wireless resonant power transfer increases the coupling distance between the implantable power receiving means and the extra-corporeal power transmitting means, reduces alignment and orientation related coupling issues, and reduces heating of the different means.
  • the implantable power receiving means and the extra-corporeal power transmitting means are arranged and configured to be capacitively loaded to form a tuned LC circuit.
  • the size, shape and dimensions of the implantable storage means and/or the implantable power receiving means are such that they can be implanted easily in different parts of the body without accidentally affecting bodily functions. More preferably, each or both are substantially elongated.
  • the elongated means may be implanted within the circulatory system, e.g. a vein or artery, without impeding fluid flow.
  • the implantable power receiving means and/or the implantable power storage means are each or both arranged and configured to be implanted within the circulatory system, preferably in a vein or an artery, more preferably within the inferior vena cava.
  • An advantage of the power receiving means and/or the implantable storage means being implanted within the circulatory system may be that heat generated from these devices can be dissipated more efficiently.
  • fluid flow within the circulatory system acts as a cooling system that dissipates heat, preventing a build up of heat at the location of these devices.
  • the heat transfer capability of the circulatory system may be 1000 times higher than that of subcutaneous tissue.
  • an electromagnetic receiving coil implanted within the circulatory system may be able to receive much higher power compared to a subcutaneous device. For example, it is envisaged that powers of up to 20 watts or greater could be utilised without excess heating of the flowing fluid within the circulatory system.
  • a receiving means for example an electromagnetic coil
  • implanting a receiving means within the cardiovascular system via surgery or other means may allow higher powers to be used during contactless power transfer.
  • a larger receiving means for example electromagnetic coil, can be utilised in the cardiovascular system compared to subcutaneous devices.
  • the implantable storage means comprises a rechargeable battery. This has an advantage of negating the need for a permanent power supply being in communication with the implantable storage means, for example a battery belt.
  • the implantable power storage means is separate from the implantable power receiving means.
  • a modular design may allow for easier maintenance of the different means, allow for easier implantation of the different means, and allow for optimum positioning of each of the means, which may depend on shape of the implanted location, need, and coupling efficiency.
  • the modular design may allow for one or more of the elements to be easily replaced if and when required. For example, some VADs are destined for permanent or semi-permanent implantation, but the battery may require replacing.
  • the modular elements may allow for specific tailoring of implant locations for specific patients, for example patients with anatomical defects or injury. Therefore, the modular design may provide for a more versatile implementation compared to current devices.
  • the implantable power storage means is integrated with the implanted power receiving means.
  • An advantage of this feature is that of compactness.
  • the power receiving means may be less prone to damage from impacts, since it may be supported by the power storage means. Further, there may be less power loss due to a shorter interconnection being required between the power storage means and the power receiving means.
  • the rechargeable power supply is made partially or completely from a biocompatible material and/or medical grade material.
  • the implantable power receiving means is positioned within a first stent or stent like structure that comprises features that enable the stent like structure to be centered within the venous system or artery using the flow of fluid.
  • the implantable power receiving means and the first stent are positioned within the circulatory system.
  • the stent has the advantage of creating a space between the vein/artery and the implantable power receiving means so that blood flow is not constricted or restricted. This has an advantage of reducing tissue damage due to friction between the implantable power receiving means and the artery wall, and localised heating of tissue around the implantable power receiving means
  • a second stent may be positioned distal from the first stent such that fluid passes through the second stent before flowing through the first stent.
  • the second stent may have a larger diameter than the first stent, resulting in a constriction between the first and second stent.
  • an intra-corporeal medical device comprising a rechargeable power supply, the rechargeable power supply comprising means for wirelessly receiving power and power storage means.
  • the intra-corporeal medical device according to the present invention can be made smaller than prior art devices due to a smaller battery being required.
  • the medical device can be wirelessly charged and, therefore, the battery can be made smaller.
  • the power receiving means and/or the power storage means are each or both integrated within the medical device. This has the advantage of compactness, and only requiring a single procedure to implant the device, which would lead to less invasive procedures for the patient. Furthermore, integration may have an advantage of reducing corrosion of the power receiving means, and preventing the power storage means from leaking into the body.
  • the power receiving means and/or the power storage means are each or both separate from the medical device. An advantage of this feature is that a modular design may allow for easier maintenance of the different means, allowing for easier implantation of the different means and allow for optimum positioning of each of the means, which may depend on shape of the implanted location, need, and coupling efficiency.
  • the modular design may allow for one or more of the elements to be easily replaced when required.
  • the modular elements may allow for specific tailoring of implant locations for specific patients, for example patients with anatomical defects. Therefore, the modular design may provide for a more versatile implementation compared to current devices.
  • the intra-corporeal medical device further comprises implantable means for supplying power received by the power receiving means to the power storage means. More preferably, the means for supplying power is a power converter, preferably an AC-DC converter.
  • an implantable wireless power receiving device for a rechargeable power supply as described above.
  • an implantable power storage device for a rechargeable power supply as described above.
  • the power storage device comprises a material that does not inhibit magnetic flux.
  • the material may be a magnetic material, air, or a non-magnetic material that does not inhibit magnetic flux.
  • the power storage device is substantially cylindrical.
  • the magnetic material extends along part of or along the whole of the longitudinal axis of the power storage means.
  • the magnetic material comprises iron and/or ferrite.
  • an extra-corporeal power transmitting device arranged and configured to supply power to a rechargeable power supply, comprising means for wirelessly transmitting power, wherein the power transmitting means is arranged and configured to transmit power to an implanted power receiving means.
  • the power transmitting means comprises an electromagnetic coil.
  • the power transmitting means and an implantable power receiving means are aligned to facilitate magnetic coupling, thereby enabling power transmission between the extra- corporeal power transmitting means and the implantable power receiving means.
  • the longitudinal axis of the electromagnetic coil is arranged and configured to be substantially parallel to the longitudinal axis of an implantable power receiving means.
  • the extra-corporeal power transmitting device further comprises means for positioning the power transmitting means relative to the implanted power receiving means to enable magnetic coupling. This may have an advantage of facilitating efficient magnetic coupling, reducing the time required for charging the implanted power receiving means, and reducing heat generated by the implanted power receiving means and the extra-corporeal power transmitting device.
  • the positioning means in use, is positioned around the torso of the patient.
  • the positioning means in use, is positioned around the abdomen of the patient.
  • a positioning means which, in use, is positioned around one of the patient's limbs.
  • the rechargeable power supply may be positioned in the arm of the patient, and the extracorporeal power transmitting means may be positioned around the arm.
  • the positioning means is substantially tubular, more preferably a wearable garment, more preferably an arm band, leg band, vest and/or belt.
  • the power transmitting means and/or the positioning means are each or both extendible.
  • each or both means may comprise or consist of an extendible material. This may have an advantage of allowing the device to form around the body of the patient without moving/slipping off the patient, which could otherwise affect the alignment of the device.
  • a method for supplying power to an intra-corporeal medical device comprising the step of implanting a rechargeable power supply in a patient.
  • the method further comprises the step of wirelessly transmitting power from an extra-corporeal power transmitting device to the implanted power receiving means.
  • the method further comprises the step of supplying the power received by the power receiving means to the power storage means.
  • the power receiving device and/or the power storage means are, in use, positioned in the circulatory system, preferably in a vein or an artery, more preferably within the inferior vena cava.
  • the method for supplying power to the intra-corporal medical device may be performed by percutaneous or transcatheter procedures.
  • figure 1 is a schematic representation of a rechargeable power supply system for an intra- corporeal medical device implanted within the body of a patient according to aspects of the present invention
  • Figures 2A and 2B illustrate experimental results relating to coupling efficiency between a receiver coil and an exciter coil according to aspects of the invention.
  • Figure 3 is a schematic representation of a further representation of a rechargeable power supply for an intra-corporeal medical device according to aspects of the present invention
  • Figure 4 is a simplified block diagram illustrating functional blocks of a rechargeable power supply for an intra-corporeal medical device according to aspects of the present invention
  • Figure 5 is a simplified block diagram illustrating functional blocks of an extra-corporeal power supply for charging the rechargeable power supply in Figs 1-3 according to aspects of the present invention
  • Figure 6 is a schematic representation of an intra-corporeal medical device comprising a rechargeable power supply according to aspects of the present invention
  • Figures 7A-7C illustrates a schematic representation of a power supply system suitable for an intra-corporeal medical device implanted within the body of a patient according to aspects of the invention.
  • Figures 8A and 8B are schematic representations of a means of positioning part of the rechargeable power supply within the circulatory system according to aspects of the invention.
  • Figure 9 is a flow chart illustrating steps for supplying power to an intra-corporeal medical device according to aspects of the present invention.
  • Figure 10 is a schematic representation of an extra-corporeal power supply for charging the rechargeable power supply according to aspects of the present invention.
  • Figures 11A and 11B are schematic representations of an alternative rechargeable power system for an intra-corporeal medical device implanted within the body of a patient according to aspects of the present invention.
  • Figure 12 is a schematic representation of an alternative implantable power storage means according to aspects of the invention.
  • Figures 13A and 13B illustrate implantable power storage means with a magnetic core and a non-magnetic core.
  • Figure 14 illustrates a solenoid with a core of non-magnetic material or magnetic material.
  • Figures 15A and 15B illustrate examples of alternative implementations for a rechargeable power system for an intra-corporeal medical device implanted within the body of a patient according to aspects of the invention.
  • the invention is described by way of examples, which are provided for illustrative purposed only. These examples should not be construed as intending to limit the scope of protection that is defined in the claims.
  • various aspects have been described with respect to the heart and the circulatory system, this is not intended to be limiting, and is merely performed to provide an example implementation.
  • any medical device implantable within the human body for example in the cardiovascular system, respiratory system, gastric system, neurological system and the like, some examples including neurostimulators, implantable defibrillators, and pacemakers, implantable drug-delivery pumps.
  • the term "means” can be equivalently expressed as, or substituted with, any of the following terms: device, apparatus, unit, structure, part, sub-part, assembly, sub-assembly, machine, mechanism, article, medium, material, appliance, equipment, system, body, or similar wording.
  • System 100 including a rechargeable power supply 120 for an intra-corporeal medical device 104, comprising implantable means 110 for wirelessly receiving power and implantable power storage means 112.
  • System 100 further comprises an extra-corporeal power supply 150.
  • the intra-corporeal medical device 104 is implanted within the heart 106 of the patient 102.
  • the medical device 104 connects the left atrium to the aorta of the patient's 102 heart 106.
  • the rechargeable power supply 120 is situated within part of the patient's 102 circulatory system, for example the patient's vena cava 108.
  • the circulatory system may include for example the left atrium, the right atrium, the left ventricle, the right ventricle, the aorta, the vena cava as well as arteries, veins and other compartments of the peripheral vascular system.
  • the rechargeable power supply 120 comprises an implanted module 110 for wirelessly receiving power (e.g. a coil), and a power storage module 112 (e.g. a rechargeable battery).
  • the implanted module 110 is operably coupled to the power storage module 112 (e.g. via a medically suitable electrical connector), and the power storage module 112 is further operably coupled to the intra-corporeal medical device 104.
  • Operably coupled' is a term used to describe a link between two or more components. The term can define a physical link between components, for example an electrical connector, or a wireless link between components, for example by inductive coupling.
  • the medical device 104 may be a mechanical circulatory support system (MCS), for example a ventricular assist device (VAD), which requires constant power in order to assist blood flow.
  • MCS mechanical circulatory support system
  • VAD ventricular assist device
  • the power storage module 112 which may be a type of rechargeable storage device such as a rechargeable battery, is arranged and configured to supply power to the intra-corporeal medical device 104.
  • the power storage module 112 may be cylindrical in shape and have dimensions suitable for allowing the device to be positioned within the circulatory system without inhibiting fluid flow within the circulatory system.
  • the power storage module 112 may have a diameter in the range of l-20mm, more preferably the power storage module 112 may have a diameter in the range of 5- 10mm.
  • the implanted module 110 is arranged to wirelessly receive power via for example a coil, from the extra-corporeal power supply 150 and couple this power to the power storage module 112 via for example a suitable cable and connector, thereby recharging or maintaining charge within the power storage module 112.
  • the coil may have dimensions similar to that of the power storage module 112, so that it can be positioned within the circulatory system without inhibiting fluid flow.
  • the coil may be designed to have a longitudinal direction arranged coaxially with the vein or artery that it is implanted within. In some examples, the coil may have a length up to or in excess of 30 centimetres, depending on the area of the cardiovascular system being used.
  • Each modular component of the rechargeable power supply 120 may comprise detachable connecting means that facilitates easy connection and disconnection of the modules. Furthermore, the interconnection between the modules is strong enough to facilitate insertion of the rechargeable power supply via a catheter based delivery method.
  • the coil 111 may have a coil length of 22mm and have an overall diameter of 9mm.
  • the coil may be formed from litz wire (10/46) that may be wound on a plastic former/bobbin.
  • the former may be hollow.
  • a magnetic material, such as an iron or ferrite bar may be positioned inside the core of the former, wherein the former insulates the coil from the magnetic material.
  • a series capacitance of around 610pF may be utilised to generate resonance in the coil at 134.6KHz.
  • the coil may have an inductance of 2.3mH and a Q of 150.
  • the coil 111 may receive 1.9W of power from a supplied power of 8.8W from the extracorporeal power supply 150.
  • a non-magnetic former such as for example plastic or ceramic, may provide support for the coil 111. This may have an advantage of reducing mechanical vibrations in the coil, which is unsupported in an air filled example. These mechanical vibrations can cause variations in the inductance generated by the coil 111.
  • Another advantage of non-magnetic cores is that they do not suffer from the same losses as magnetic cores when operating at high frequencies, for example some resonant frequencies.
  • a magnetic core within the former, for example iron or ferrite, may increase the inductance of the coil 111 compared to a non-magnetic or air filled core. This may have an advantage of reducing the size of the coil 111 that is required.
  • a magnetic core such as ferrite concentrates the magnetic flux through the coil 111 where it can be efficiently harvested.
  • the extra-corporeal power supply 150 comprises a coil 152, for example an electromagnetic coil, electrically couplable to a power source 154.
  • the coil 152 is arranged and configured around the exterior of the patient 102, wherein the windings of the coil 152 are positioned such that they substantially coil around the torso of the patient 102.
  • the windings of the coil may be positioned in close proximity to each other or be positioned as illustrated with respect to coil 152, wherein the coil has a longitudinal direction with respect to the patient 102.
  • the implanted module 110 may also comprise a coil 111 that is operably coupled to the power storage module 112.
  • the coil 111 is also implanted within the vena cava 108 of the patient 102.
  • the coil 111 of the implanted module 110 also comprises windings, which are arranged in a coaxial position relative to the windings of the coil 152 of the extracorporeal power supply 150. This has an advantage of allowing efficient magnetic coupling between the coils.
  • the coil 152 may be formed from litz wire (105/40) with approximately 40 turns with a circumference suitable to be positioned around a torso of a patient. A series capacitance of around 785pF may be utilised to generate resonance in the coil at 134.6KHz.
  • the coil 152 may have an inductance of 1.78mH with an 8 ohm resistance and a Q of 190.6.
  • the power source 154 of the extra-corporeal power supply 150 couples power to the coil 152.
  • the coil 152 will subsequently produce a magnetic field that is strong enough to be coupled to the coil 111 of the implanted module 110, which is positioned distal from the coil 152.
  • magnetic flux generated by the coil 152 will be produced in the 'y' direction of axis 170.
  • the coil 111 is arranged and configured to receive the magnetically coupled power from the coil 152, and supplies this power to the power storage module 112. This is achieved by aligning the coil 111 so that it is parallel to the coil 154, for example the coil 111 is arranged so that it couples the magnetic flux generated in the 'y' direction according to axis 170.
  • non-radiative energy can be transferred between power supply 154 and power storage module 112 in the form of coupled magnetic flux, via coils 111 and 152.
  • This has an advantage of allowing the power storage module 112 implanted within the vena cava 108 of the patient 102 to be charged without the need for surgical intervention.
  • the rechargeable power supply 120 comprises modular components in the form of a modular implanted module 110 and a modular power storage means 1 12, for example a cylindrical rechargeable battery and a solenoid.
  • Providing a modular system may allow for the various components of the rechargeable power supply 120 to be maintained without requiring surgical removal of the entire rechargeable power supply 120 or the medical device 104.
  • each modular portion of the rechargeable power supply 120 may be implanted or removed via percutaneous means, thereby simplifying the procedure, reducing patient recovery times and reducing the chance of infection.
  • the modular design of the rechargeable power supply 120 may allow it to be situated within small areas, such as veins, arteries or the inferior vena cava, whilst still facilitating blood flow in those areas.
  • Positioning the rechargeable power supply 120 within the intravascular system allows for greater flexibility in terms of positioning. Further, unlike subcutaneous devices, positioning the rechargeable power supply 120 within the intravascular system may make it less prone to damage from impacts to the patient's body.
  • the modular arrangement of the rechargeable power supply 120 also has an advantage of allowing the positioning of some components outside of the circulatory system.
  • an optional controller that is arranged to control operation of the rechargeable power supply 120 for example controller 315 from FIG. 3, may be positioned outside of the vena cava 108. This has an advantage of positioning larger modules of the rechargeable power supply outside of the circulatory system so that the fluid flow rate inside the vena cava 108 is not reduced due to it being obstructed or constricted.
  • the modular arrangement of the rechargeable power supply 120 also has the advantage of allowing optimal positioning of the coil 111 with respect to the coil 152 of the extra-corporeal power supply 150.
  • different connector lengths that couple the coil 111 to the modular arrangement can be utilised so that the coil 111 is optimally aligned in the vena cava with respect to the coil 152.
  • the coil 111 and/or implanted module 110 may be positioned within the circulatory system, for example the vena cava 108, and the remaining modules of the rechargeable power supply 120 may be positioned outside the circulatory system. This may have an advantage of maintaining optimum fluid flow around the coil 111 and/or implanted module 110 such that localised heating of the coil 111 can be reduced by convection.
  • the solenoid and the rechargeable battery may be maintained in their desired position via a cable that electrically connects them to each other and/or the medical device 104.
  • a separate tether may be used in order to anchor the various components of the rechargeable power supply 120 to the relevant part of the circulatory system and/or medical device 104.
  • the example embodiment relating to figure 1 has shown the rechargeable power supply
  • the coil 111 and/or coil 152 may be concentrically wound coils (flat/planar coils), or helical coils (solenoid). In the case of flat coils, the position and/or orientation of the coils 111 and 152 may need to be changed so that the generated magnetic flux can be efficiently coupled.
  • a potential advantage of a helical coil may be that it is suitably wide enough to prevent it rotating out of its 'y' axis plane according to axis 170, when implanted within the vena cava 108 for example. Further, due to the direction of magnetic flux, the helical coil can freely rotate about the y axis within the vein without becoming misaligned. The size of the coil is such that it does not inhibit fluid flow within the circulatory system.
  • An advantage of a flat coil is that it can be easily integrated on the power storage means, and that it takes up less area in the vein. However, this type of coil may require stabilising means in order to keep it in optimum alignment with generated magnetic flux from the extra-corporeal transmitting device.
  • the rechargeable power supply 120 may not comprise a power storage module 112.
  • the implanted module 110 may receive power from the coil 152, via coil 111, and supply the power directly to the medical device 104.
  • the implanted module 110 may power the medical device 104 and/or charge the power storage means 112.
  • the medical device 104 could be powered from the implanted module 110 and/or the power storage means 112.
  • a further advantage of the helical coil is that it is alignment tolerant when receiving power from the coil 152.
  • Experimental results illustrated in figure 2 indicate that coupling efficiency between a helical coil, for example coil 111, and coil 152 can be maintained above 60% when the position of the coil 111 is moved radially from a sidewall within coil 152 to the central point inside of the coil 152 (in the 'x' direction according to axis 170).
  • experimental results have indicated that coupling efficiency between the coil 111 and the coil 152 can be maintained above 60% when the position of the coil 111 is moved longitudinally within the boundaries of the coil 152 in the 'y' direction according to axis 170.
  • This alignment tolerance results in less tuning being required when initially configuring the rechargeable power supply 120 in combination with the extra-corporeal power transmitting device 150.
  • Figure 2A illustrates the longitudinal alignment coupling efficiency of coil 111 with respect to coil 152.
  • Figure 2B illustrates the radial alignment coupling efficiency of coil 111 with respect to coil 152.
  • a simplified schematic representation of the experimental apparatus 200 is illustrated, which comprises a cylindrical cardboard tube 202 of a diameter of approximately 30cm and a length of approximately 20cm.
  • Coil 152 is wound around tube 202 to form a strip, the coil 152 having a strip width of approximately 8cm.
  • the longitudinal centre point of the coil 152 (centre point of the width of the strip) is aligned with the longitudinal centre point of the tube 202.
  • the coil 111 is positioned at the centre of the tube 202 and measured at 1 cm increments from 0cm to 20 cm in a longitudinal direction as illustrated in figure 2A.
  • the measurement results are shown on graph 250, which compares the longitudinal distance on the 'X' axis with coupling efficiency on the ⁇ ' axis.
  • Maximum coupling efficiency between coils 152 and 111 is achieved at a distance of 10cm, which relates to the central point of the strip width of coil 152.
  • Coupling efficiency of over 60% is achieved ⁇ 3 cm from the central point of the diameter of coil 152, resulting in an alignment tolerant system.
  • Figure 2B illustrates the radial alignment coupling efficiency of coil 11 1 with respect to coil 152.
  • the longitudinal centre point of the coil 111 is aligned with the central point of coil 152.
  • the coil 111 is positioned at an edge of the tube 202 and measured at 1cm increments from 0cm to 15cm (central point of tube 202).
  • the measurement results are shown on graph 260, which compares the radial distance on the 'X' axis with coupling efficiency on the ⁇ ' axis.
  • a coupling efficiency of over 60% can be achieved throughout the tested range, except within a lcm band from the edge of the tube 202. This results in an alignment tolerant system, which may require a spacer so that the coil 111 is not positioned within lcm of an edge of the coil 152.
  • FIG 3 a schematic representation of an integrated rechargeable power supply 320 is illustrated, comprising a power storage module 312 and a coil 311 that surrounds the power storage module 312.
  • the integrated rechargeable power supply 320 may replace the rechargeable power supply 120 of figure 1.
  • the operation of the integrated rechargeable power supply 320 is similar to the operation described in figure 1 for the rechargeable power supply 120.
  • the coil 311 is arranged as a longitudinal coil (solenoid) that spirals along the entire length of the power storage module 312. It should be noted that the coil does not need to spiral along the entire length of the power storage module 312 to function. However, increasing the length of the spiral may have an advantage of increasing coupling area between the coil 311 and the coil 111 of the extra-corporeal power supply from figure 1.
  • the coil 311 may be formed from a number of solenoids that are coupled to the power storage module 312. This may have an advantage of improving robustness and efficiency of coupling in case one of the coils becomes damaged or misaligned.
  • a simplified block diagram of a rechargeable power supply 400 for example, the rechargeable power supply 120/320 from figures 1 and 3 is illustrated.
  • the rechargeable power supply 400 comprises a means for wirelessly receiving power 402, for example a coil arranged to receiving magnetic flux 404 generated by an extra-corporal power supply (not shown), an optional capacitive element 406, which in this example embodiment is coupled in parallel with the means for wirelessly receiving power 402, a means for supplying power 408, optional smoothing means 410, and power storage means 412.
  • the various blocks may represent modular or integrated elements of the rechargeable power supply 400.
  • the optional capacitive element 406 is coupled in series with the means for wirelessly receiving power 402.
  • the series combination results in lower impedance at resonance so that a coil, such as coil 152 of the extra-corporeal power supply 150, can be powered by amplifiers with a supply voltage of around 18Vrms. This has an advantage of reducing the supply voltage required to power the coil 152 because of the reduced impedance in the rechargeable power supply 400.
  • the means for wirelessly receiving power 402, in this example a coil, may be aligned such that it efficiently couples magnetic flux 404 generated from the extra-corporeal power supply, for example in the form of inductive coupling.
  • the optional capacitive element 406 may be arranged to capacitively load the coil to form a tuned LC circuit.
  • the received magnetic flux may be generated from an extra-corporeal power supply also comprising a capacitively loaded tuned LC circuit, wherein both coils may be arranged to resonate at the same common frequency. This may have an advantage of increasing the magnetic coupling distance between the coils, increase efficiency of coupling, and reduce heat generated in the coils of the rechargeable power supply 400 and the extra-corporeal power supply.
  • the common frequency may include frequencies that generate minimum heating of human body tissues.
  • the common frequency may be at least lMHz.
  • the means for wirelessly receiving power 402 may be operably coupled to the means for supplying power 308.
  • the means for supplying power 408 receives AC power of a certain frequency and converts this AC power into DC power.
  • the means for supplying power 408 may comprise either a full or a half wave rectifier, arranged to convert the AC power to DC power.
  • the means for supplying power 408 may be optionally coupled to a smoothing means 410, which may be arranged to reduce voltage and/or current ripple before the resultant DC power is coupled to the power storage means 412.
  • smoothing means 410 may comprise additional capacitance and inductance in order to reduce ripple prior to the DC power being coupled to the power storage means.
  • a control means 415 may be arranged and configured to control charging of the power storage means 412.
  • the control means 415 may be coupled to the means for supplying power 408, the power storage means 412 and optionally the smoothing means 410.
  • the control means 415 may determine the amount of charge stored in the power storage means 412 and regulate the means for supplying power 408 in order to efficiently charge and/or prevent overcharging of the power storage means 412.
  • the control means 415 may be arranged and configured to wirelessly transmit information via a wireless link 416 to the extra-corporeal power supply (not shown) to indicate if the power storage means 412 is fully charged. In an example, this may be achieved using a short range wireless interconnection, such as Bluetooth or near field communication (NFC).
  • the control means 415 may comprise at least a processor, arranged to control the charging of the power storage means 412. The processor may also be arranged to prevent overcharging of the power storage means.
  • the wireless link 416 may be utilised to transmit diagnostic information to other extra-corporeal devices, or be utilised to update/change the operation of the rechargeable power supply 400 and/or an interconnected medical device.
  • the wireless link 416 may be arranged to update software located in a memory within the control means 415 for controlling the processor.
  • FIG 5 a simplified block diagram of an extra-corporeal power transmitting device 500, for example, the extra-corporeal power transmitting device 150 from figure 1 is illustrated.
  • the extra-corporeal power supply 500 comprises a power supply 502, arranged to supply either DC or AC power.
  • the output of the power module 502 may be coupled to an optional means 404 for supplying the output power to means 506 for wirelessly transmitting power.
  • the means 504 for supplying the output power may comprise a DC/ AC converter, arranged to convert the DC power to AC power.
  • the means 504 may supply an alternating current to the means 506, which may be a coil, to enable the means 506 to wirelessly transmit power.
  • the AC current causes the coil to generate magnetic flux that is emitted by the means 506.
  • An optional capacitive element 508 may be arranged in parallel with the means 506 in order to capacitively load the means 506 to form a capacitively loaded tuned LC circuit.
  • the tuned LC circuit may resonate at a frequency substantially the same as a receiving coil of a rechargeable power supply implanted in the body of a patient, thereby allowing resonant inductive coupling.
  • the means 504 may reduce the power via a passive device, such as a resistive network, and/or an active device, such as a switched mode power supply, in order to provide suitable AC power to the means 506.
  • the means 504 may comprise an AC/DC converter, such as for example a rectifier arrangement, that is configured to convert the received AC power into DC power, before reconverting to AC power via a DC/AC converter.
  • An optional control module may be coupled to the AC/DC converter and the DC/ AC converter in order to control the output power supplied to the means 506.
  • a capacitive element 508 may be arranged in parallel with the means 506, as discussed above.
  • the optional capacitive element 508 is coupled in series with the means 506. The series combination results in a lower source impedance. If this example embodiment is combined with the embodiment of the rechargeable power supply 400 having a series capacitance, a low supply voltage of around 18 Vrms can be used in the extracorporeal power transmitting device 500, resulting in detected voltages within the rechargeable power supply 400 of around 20Vrms to 70Vrms. These voltages are at a level that allows for easier power management by the rechargeable power supply 400.
  • the means 506 may comprise a coil, which is configured to be positioned around the body of a patient, preferably the abdomen of the patient.
  • the coil may be comprised within a positioning means, which may be substantially tubular. The patient may be able to slip the tubular positioning means around the abdomen, aligning the coil with an implanted medical device.
  • the positioning means may be designed to be positioned around a limb of the patient, for example in the form of a bracelet. An implanted medical device may also be implanted within the limb in order to receive power from the bracelet shaped positioning means.
  • the power module 502 is arranged to supply mains power to the means 504, which comprises an AC- AC converter arranged to reduce the power to a level suitable for transmission by the means 506.
  • the means 506 in this example is an electromagnetic coil that is, in use, positioned around the torso of a patient such the windings of the coil wrap around the torso of the patient.
  • the electromagnetic coil is positioned such that it can efficiently couple power to a coil implanted within the patient's torso.
  • the electromagnetic coil may comprise closely wound windings that approximate a planar coil.
  • the windings may be arranged such that they form a solenoid around the patient's torso, wherein the longitudinal axis of the solenoid is coaxially arranged with the longitudinal axis of the patient's torso.
  • FIG 6 a schematic representation of an intra-corporeal medical device 600 comprising a rechargeable power supply is illustrated.
  • the medical device 600 may comprise the rechargeable power supply 400 illustrated in figure 4.
  • the medical device 600 may be implanted within a patient, for example implanted within the patient's heart 650. In other examples, the medical device 600 may be implanted within a patient's head or limbs.
  • the medical device 600 may comprise a number of application specific modules 602, and the rechargeable power supply.
  • a coil 604 may be located at the exterior 606 of the medical device 600. This may have an advantage of increasing the coupling efficiency of the coil.
  • the coil 604 may be covered with a medically-safe material such as silicon or latex in order to prevent corrosion of the coil 604.
  • the application specific modules 602 and the remaining components of the rechargeable power supply may be arranged within a magnetic shield layer 620, arranged to protect the components of the medical device 600 from magnetic energy received by the coil 604 or other devices that may emit magnetic fields.
  • the coil 604 may be positioned within the medical device 600, negating the need for covering the coil 604 in a medically-safe coating.
  • the coil 604 may be positioned in a cavity situated between the exterior of the medical device 600 and the shield layer 620.
  • the coil 604 may be coated with a biocompatible coating, for example Parylene.
  • the coil 604 may be coated with a hydrophobic coating and/or friction reducing coating to help with implantation. The coating may also provide for electrical isolation, heat transport and coagulation prevention.
  • the medical device 600 comprising the coil 604 may need to be aligned correctly with an extra-corporeal power supply (not shown) in order to maximise magnetic coupling.
  • Stabilising means 622 may be optionally utilised on the medical device 600 in order to prevent the medical device from rotating/changing orientation within the patient.
  • the coil 604 in this example is positioned perpendicular to the direction of fluid flow in the patient's heart 650. This may be so that the coil can be correctly aligned with the extra-corporeal power supply (not shown). Equally, the medical device 600 can be positioned such that the coil 604 is positioned parallel with the direction of fluid flow.
  • the stabilising means 622 may be arranged to anchor the medical device 600 in a preferred orientation in order to maximise coupling between the coil 604 and the extra-corporeal power supply (not shown).
  • the stabilising means 622 may comprise one or more anchors that are able to maintain the position of the medical device 600 without impeding fluid flow.
  • the stabilising means 622 may comprise one or more spring loaded securing arms that can be deployed once the medical device is in the correct position/orientation.
  • the stabilising means 622 may also comprise a mesh, which is arranged to anchor the medical device 600 to the wall of the heart 650.
  • FIG. 7A illustrates a schematic representation of a power supply system 700 suitable for an intra-corporeal medical device implanted within the body of a patient.
  • the intra-corporeal medical device is a VAD 702, which is implanted in the patient's heart 704.
  • the VAD 702 is connected to a driveline cable 706 via an interconnect 708.
  • the driveline cable 706 may be positioned partially within the heart and in the circulatory system, for example in the vena cava, or entirely in the circulatory system 710 as depicted in figure 7.
  • the driveline cable 706 is coupled to a controller 712 via a further interconnect 714, which may be the same or different as interconnect 708.
  • the controller 712 is operable to control aspects of the VAD via the driveline.
  • the driveline may comprise a tension wire (not shown) to strengthen the driveline 706 and prevent damage to wiring within the driveline 706 that connects the controller 712 to the VAD 702.
  • the controller 712 is powered by an implanted module that comprises a coil 716.
  • the implanted module comprising the coil 716 is also utilised to power the VAD 702 via the drive line 706.
  • the implanted module comprising the coil 716 may charge a battery pack 718 as well as supplying power to the controller 712.
  • the battery pack 718 may be used as a back-up power supply and/or a means for supplementing power supplied to the VAD 702 from the module comprising the coil 716.
  • the coil 716 may be positioned within a stent like structure comprising braiding or other features to enable the coil 716 to be positioned centrally within the circulatory system 710 using the flow of fluid.
  • the coil 716 may be coated in a material that allows fluid to flow around the coil 716 without the need for the stent like structure.
  • the battery pack 718 is arranged to supply between approximately 14 volts to 30 volts. It is envisaged that the battery pack 718 comprises multiple rechargeable cells each having an approximate voltage of 3.7 volts. The cells are connected in series to reach the desired voltage.
  • the rechargeable cells could be 4 x AAA sized batteries.
  • Lilon rechargeable chemistry can be used. An advantage of using Lilon is that the rechargeable cells are smaller for a given voltage rating compared to other battery technologies, which means that these cells have an advantage of increased flexibility and can be implanted more easily in series within the vasculature.
  • the driveline 706, module comprising the coil 716 and the battery pack 718 may be encased in a delivery means 720.
  • the delivery means 720 may have an advantage of facilitating easier delivery and positioning of the power supply system 700 if implanted by a catheter based delivery method.
  • the delivery means 720 is a catheter system that pushes elements of the power supply system 700 into position.
  • the components of the power supply system 700 may already be connected to each other prior to delivery.
  • the catheter system could sheath the entire train of modular components of the power supply system 700 and release each constituent component one at a time into the desired position.
  • the VAD 702 could be delivered to its desired location and then the remaining modular components of the power supply system 700 could be surgically connected to the VAD 702. Magnetic interconnections could be utilised to connect the modular elements of the power supply system 700. It is important that the VAD 702 and the driveline 706 have a hermetic seal to prevent fluid ingress.
  • the VAD 702 may be connected to the driveline cable 706 prior to insertion of the device into the circulatory system 710. In such an example illustrated in figure 7B thread it may be possible to weld a cap 722 over the connection interface 726 between the VAD 702 and the driveline cable 706.
  • the cap 722 may comprise a non reactive metal tube that can be positioned over and welded onto the VAD 702 and driveline 706 in order to form a hermetic seal and to strengthen the interface 726 such that movement of the VAD 702 and/or driveline 706 does not strain the connections.
  • the VAD 702 may be connected to the driveline cable 706 after the VAD has been inserted into the circulatory system 710.
  • an interconnection is required that can engage and disengage with the VAD 702 and the driveline 706 within the circulatory system 710, whilst providing a hermetic seal to prevent fluid ingress to the connection interface 726.
  • Such an interconnection 724 is illustrated in figure 7C.
  • Interconnection 724 may comprise a suction port or a magnetic mounting means, for example, which facilitates a connection between the VAD 702 and the driveline 706 whilst providing a hermetic seal between said components.
  • the hermetic seal may also be implemented via a hermetic ceramic feed-through on the VAD 702 and the driveline 706.
  • the driveline 706 may have an interconnection comprised of biocompatible material and having a screw, press fit or other similar type of connection to the VAD 702.
  • controller 712 may be connected to the VAD 702 directly, thereby negating the need for a driveline 706.
  • the part of the power supply may comprise the coil 111, which is situated within a vein or artery 802.
  • the coil 111 is positioned within a stent 804, which creates a space between the walls 806 of the vein or artery 802 and the coil 111 so that fluid 708 can flow between the coil 111 and the walls 806.
  • This has an advantage of preventing the coil 1 11 from blocking fluid flow and reducing the velocity of fluid flow in the vein or artery 802, which is indicated by arrows 810.
  • the stent 804 is designed such that the passing fluid prevents the temperature around the coil 111 from exceeding 2°C above ambient fluid temperature.
  • FIG 8B another example of a schematic representation of part of the power supply from figures 1 and/or 7 is illustrated in the circulatory system of the patient.
  • a larger diameter stent 812 is positioned before the coil 111 with respect to the direction of fluid flow.
  • the flow of fluid indicated by arrows 814 is constricted at area 816, which has an advantage of increasing the velocity of the flow of fluid around the coil 111.
  • the increased velocity fluid passing over the coil 111 can remove more heat.
  • the coil 111 may be tethered to the stent 804 to prevent the stent 804 from moving outside of the confines of the stent 804.
  • the embodiments referring to the stent can be combined with the apparatus of figure 1 and/or 7.
  • some or all of the components 702, 706, 708, 712, 714, 716, 718 may be situated within a stent according to figure 8 A and/or 8B to facilitate homogeneous blood flow and/or increased velocity fluid flow.
  • a flow chart illustrating steps for supplying power to an intra- corporeal medical device, such as intra-corporeal medical device 600, is illustrated.
  • an implantable medical device for example an LVAD
  • the LVAD is implanted into a patient.
  • the LVAD may be implanted via a percutaneous insertion device, and arranged between the patient's left atrium and aorta.
  • an implantable rechargeable power supply for example the implantable power supply 400 from figure 3, is implanted in the patient.
  • the rechargeable power supply may comprise modular components, in which case subsequent steps may be required to implant the rechargeable power supply.
  • a rechargeable power storage device such as a rechargeable battery
  • the rechargeable power storage device may be implanted in a different area of the patient's body compared to the medical device.
  • the rechargeable power storage device may be implanted in the inferior vena cava, and connected to the medical device via a suitable length connector.
  • a means for wirelessly receiving power for example an electromagnetic coil
  • the coil may be implanted in a different area of the patient's body and electrically connected to the rechargeable power storage device via a suitable electrical connector.
  • Positioning the coil in a different location to the medical device and/or the rechargeable power storage device may have an advantage of allowing optimum positioning of the medical device and/or the coil.
  • the coil may need to be implanted in a specific location in order to maximise energy transfer, which may be a different location and orientation to the medical device.
  • an extra-corporeal power transmitting device for example the extra-corporeal power transmitting device 150 from figure 1, may be positioned around the abdomen of the patient.
  • AC power is supplied to the extra-corporeal power transmitting device, which is supplied to a coil surrounding the patient.
  • the current in the coil generates a magnetic field, which may be at a medically safe resonant frequency that is transmitted to the implanted coil of the rechargeable power supply through the patient's body.
  • the implanted coil of the rechargeable power supply couples the generated magnetic field, in the form of magnetic flux.
  • the means for wirelessly receiving power may comprise a number of coils for receiving the transmitted field.
  • the received magnetic flux is converted to DC power, via for example a suitable AC/DC converter, and supplied to the rechargeable power storage device.
  • the rechargeable storage device may receive the DC power and be appropriately charged, or the rechargeable power storage device may forward the DC power onto the medical device without charging the power storage device if, for example, the power storage device is fully charged.
  • the rechargeable power supply may comprise a modular design. This may allow the device to be implanted in different areas of the patient's body, optimising the effectiveness of the device. Furthermore, the rechargeable power supply may be minimally invasive due to its size and modular design, which may allow it to be implanted in a similar manner to the medical device. Furthermore, the coil of the wireless receiving device may be elongated (a solenoid/helical coil) and aligned such that it substantially reduces magnetic coupling alignment issues. The coil may be formed from a number of coils arranged in different orientations with respect to the extracorporeal transmitting device. This may reduce magnetic coupling alignment issues.
  • the extra-corporeal power supply 1000 comprises a power supply 1002, arranged to supply AC or DC power to a means for wirelessly transmitting power 1004, via a suitable cable 1006.
  • the means for wirelessly transmitting power 1004 is arranged and configured to transmit power to an implanted power receiving means of the rechargeable power supply 400 from figure 4.
  • the means for wirelessly transmitting power 1004 comprises an electromagnetic coil.
  • the windings of the electromagnetic coil can be housed in a tubular positioning means 1008.
  • the tubular positioning means 1008 may be arranged to form a hollow cylinder, wherein the hollow cylinder is positioned around the torso/abdomen of the patient, such that the longitudinal axis of the cylinder is coaxially aligned to the longitudinal direction of the patient's torso.
  • the windings of the electromagnetic coil are arranged and configured to be wound around the body of the hollow cylinder, such that the windings are coiled around the circumference of the cylinder.
  • the windings of the coil may be arranged such that they have no longitudinal direction, as illustrated with respect to coil 1010. In this case, the coil 1010 needs to be positioned in close proximity to a respective power receiving device.
  • the windings of the coil may form a helix, as illustrated by coil 1020, which is arranged around the body of the tubular positioning means 1008.
  • Current applied to the helix which can also be thought of as a solenoid, produces a magnetic filed that runs perpendicular to the orientation of the windings of the helix.
  • the tubular positioning means 1008 may optionally be used to form a wearable garment that supports/houses the electromagnetic coil.
  • the electromagnetic coil may itself be formed from a continuous solenoid, as illustrated by coil 1030 to form an extendible element.
  • the garment comprising the electromagnetic coil comprises elasticity, meaning that the garment may fit securely around a patient's abdomen, for example, without extra securing means being required.
  • the coil 1030 may comprise spring like qualities, allowing it to be stretched around the patient's torso, within the garment, and subsequently attempt to return to its original shape thereby securing itself to the patient.
  • the windings of the coil may be arranged as illustrated in coil 1040, wherein the windings are bent to produce another coil with spring like qualities.
  • the examples illustrated with respect to the coil 1030 and coil 1040 can be arranged in either a helical or planar arrangement as illustrated for coils 1010 and 1020.
  • the tubular positioning means 1008 may be formed into a bracelet for wearing around an arm of a patient. This may be particularly advantageous if the rechargeable power supply 400 is positioned within the arm of the patient.
  • tubular positioning means 1008 may be formed into any suitable means for wearing around any part of the patient's body.
  • the rechargeable power supply 400 may also be located anywhere within the patient's circulatory system, depending on application.
  • FIG. 11A and 11B an alternative schematic representation of a rechargeable power supply system for an intra-corporeal medical device implanted within the body of a patient is illustrated.
  • the remainder of the rechargeable power supply has not been illustrated as its functionality is the same as that described for figure 1 , unless stated otherwise with respect to figures 11 Aand 1 IB.
  • An axis 1160 has been illustrated with respect to figures 8a and 8b in order to help explain the direction of magnetic coupling.
  • an implantable means 1102 for wirelessly receiving power is situated within a patient 1150.
  • the implantable means 1102 may be a planar coil or a helical coil/solenoid.
  • An extra corporeal power transmitting device 804 may be positioned at a location adjacent to and or/on the patient's 1150 abdomen and/or back, and comprise at least one means 1106 for wirelessly transmitting power.
  • means 1106 for wirelessly transmitting power may comprise a planar coil that is aligned in such a way that magnetic flux 1105 produced in this coil will propagate in the x direction according to axis 1160.
  • the implantable means 1102 is aligned such that it can effectively couple the magnetic flux 1105.
  • the implantable means 1102 is aligned co axially with the means 1104 for wirelessly transmitting power along the x axis 1160.
  • figure HA has been illustrated with two means 1104 for wirelessly transmitting power, it may be that only one means is required, if it is aligned so that magnetic flux can be coupled to the implanted means 1102.
  • situating at least two means 1106 within the direction of magnetic flux may increase coupling efficiency compared to a single means.
  • implantable means 1102 may comprise a number of coils with different alignments/orientations with respect to the direction of the generated magnetic flux. This may allow the implantable means 1102 to still efficiently couple the transmitted magnetic flux even if one or more of the coils are not aligned in order to efficiently couple the transmitted magnetic flux.
  • Figure 1 IB essentially operates in the same way as figure 11 A.
  • the means 1106b for wirelessly transmitting power have been arranged such that the magnetic flux 1105b generated propagates in a 'Z' direction according to axis 1160. Therefore, implanted means 1102b is aligned to efficiently couple magnetic flux generated from means 1106b.
  • means 1106b may comprise one or more planar coils.
  • the embodiments of figures 11 A and 1 IB can be combined. This may result in an implanted means 1102 capable of receiving magnetic flux in an 'X' and 'Z' direction, which may increase the coupling efficiency and may lessen the requirement for correct alignment in order to efficiently coupe magnetic flux from the means 1106.
  • the dotted means 1106b signifies that this means 1106b is positioned on the back of the patient.
  • An advantage of the planar means 1106 may be that they can be incorporated into a garment or simply positioned in a coupling position without the patient having to position the windings of the coils around their abdomen.
  • example embodiments of the invention have focussed on the medical device being implanted in the heart, it is envisaged that the medical device can be implanted at any required location in a patient, for example the patient's head, lungs, gastric system etc.
  • An advantage of the modular design of the rechargeable power supply may be that in a specific example regarding the head, the coil could be situated away from the patient's brain, for example in the neck, thereby potentially reducing any undesirable heat generation from sensitive areas of the patient's body.
  • example embodiments have focussed on the rechargeable power supply being situated within the circulatory system, this is not essential and the rechargeable power supply can be an integral part of the medical device, or be situated within the patient in a location other than in the circulatory system.
  • the power storage module 312/112 described in relation to figure 3 and figure 1 may be a form of rechargeable battery, for example an electrochemical storage battery comprised of known battery chemistries. Further, the power storage module may be a type of capacitor or super capacitor, which may be more tolerant to repeated charge and discharge cycles but require more frequent charge cycles.
  • FIG. 12 illustrates a schematic representation of an alternative implantable power storage means 1200.
  • the alternative implantable power storage means 1200 may be used in place of the implantable power storage means 112/312 described in the above mentioned examples
  • power storage means 1200 comprises a cylindrical shaped battery 1202 with a hollow core 1204.
  • the hollow core may extend along part or a whole of the longitudinal axis of the power storage means 1202.
  • the diameter of the hollow core 1204 may be implementation specific.
  • the battery 1202 may be folded to form a cylinder with a hollow core.
  • the position of the hollow core 1204 may be offset from the centre point of the cylindrical battery 1202. Further, the hollow core 904 may be formed from a number of smaller hollow cores (not shown). A hollow core, which may be air-filled, may prevent magnetic flux inhibiting material of the battery interfering with magnetic flux generated by a coil in close proximity to the battery.
  • the cylindrical shaped battery 1202 may be a rechargeable battery, comprising one of a lead-acid battery, a nickel-cadmium battery, nickel-metal hydride battery, lithium-ion battery or a lithium-ion polymer battery.
  • a particular advantage of lithium-ion polymer batteries is that they can form easily into different shapes during manufacture.
  • the power storage means 1200 may comprise or consist of a super- capacitor
  • the hollow core 1204 may be filled, or partially filled, with a magnetic material.
  • the magnetic material may comprise ferrite, iron, or any other magnetic material suitable for inductor cores.
  • the magnetic material may enhance the inductance of a coil in proximity to the battery.
  • the hollow core 1204 may be filled, or partially filled, with a non- magnetic material that does not interfere with the inductance of a coil in proximity to the battery (i.e. does not inhibit magnetic flux).
  • This material may be a plastic, ceramic or other nonmagnetic material that does not interfere with the inductance of a coil in proximity to the battery.
  • a magnetic core may be undesirable due to the frequencies being used.
  • a 'filler' may be utilised in these instances to reduce ingress of bodily fluid into the core 904.
  • Current batteries may contain material that would affect magnetic flux (magnetic flux damaging materials) generated in a coil in close proximity to the battery.
  • the battery material may be replaced/combined with a magnetic flux enhancing material.
  • the battery chemistry may be supplemented or replaced by a magnetic flux enhancing material.
  • the power storage means 1200 may comprise magnetic material other than at its core.
  • the magnetic material may surround a periphery of the power storage means 1200.
  • an outer insulating layer may be required to insulate the magnetic material from a coil being wrapped around the power storage means 1200.
  • the power storage means 1200 may not comprise a hollow core.
  • the power storage means 1200 may optionally be coated with a biocompatible coating.
  • This coating may provide on or more of; electrical insulation, heat transport coagulation prevention, friction reduction and hydrophobic qualities.
  • coating the power storage means 1200 in a friction reducing coating may allow for easier implantation.
  • the coating may be Parylene.
  • Figure 13 illustrates two examples of the implantable power storage means 1200 in conjunction with a solenoid 1306. As discussed above, the power storage means 1200 can replace implantable power storage means 312 of figure 3.
  • Figure 13A illustrates power storage means 1300 implemented with a hollow air core 1304.
  • a solenoid 1306 is positioned around the circumference of the power storage means 1300, with the direction of the windings being perpendicular to the direction of the hollow air core 1304.
  • Illustrative magnetic field lines 1308 have been shown to indicate the direction of the generated magnetic field when the power storage means 1300 is in use.
  • the hollow air core 1304 may be filled with a non-magnetic material, such as plastic or ceramic.
  • Figure 13B illustrates power storage means 1300 implemented with a magnetic core 1312.
  • the magnetic core may be iron, ferrite, or any other suitable magnetic material.
  • the magnetic core increases the inductance of solenoid 1306, by increasing the magnetic field due to the core's higher magnetic permeability.
  • An advantage of using a magnetic core may be that the size of the solenoid, or the power it needs to receive, can be reduced when compared to a device not using a magnetic core. This may reduce localised heating of tissues during use.
  • the power storage means 1300 comprising the magnetic core 1310 is able to achieve higher inductance compared to the power storage means in figure 13 A.
  • the magnetic core 1310 may be a laminated or ferrite core in order to reduce core losses associated with utilising high frequencies.
  • Figure 14 illustrates a specific example described with respect to figure 1.
  • Figure 14 illustrates the implantable power storage module 112 operably coupled to implantable module 110 for wirelessly receiving power.
  • the implantable module 110 is a solenoid.
  • the solenoid is wound around a former/bobbin 1400.
  • the former 1400 comprises an insulating material and can be hollow or filled.
  • a magnetic material such as an iron or ferrite bar, can be positioned within the former.
  • the magnetic material is insulated from the coil by the former.
  • the magnetic material increases the magnetic field of the solenoid in use, due to the higher magnetic permeability of the magnetic material compared to air or nonmagnetic materials.
  • FIG. 15A an alternative schematic representation of a rechargeable power supply system for an intra-corporeal medical device implanted within the body of a patient is illustrated.
  • an intra-corporeal device 1503 is positioned within a patient lying on a bed.
  • an extra-corporeal device 1502 is positioned in a mattress 1501 of the bed.
  • the extra-corporeal means does not have to be positioned within a garment worn by the patient.
  • the extra-corporeal device 1502 can be larger, because it does not need to be worn by the patient.
  • the extra-corporeal device 1502 may have a higher power transmitter, allowing magnetic coupling with the intra-corporeal device 1503 at increased separation distances compared to other embodiments of the invention.
  • An advantage of this arrangement may be that the patient can charge the intra-corporeal device 1503 without having to wear a garment comprising the extra-corporeal device 1502.
  • the extra-corporeal device 1502 could be positioned in an item of furniture, such as a chair.
  • the extra-corporeal device 1502 is further illustrated within a room 1505, and/or in a wall 1504.
  • the patient can charge the intra-corporeal device 1503 without being confined to a bed, or chair for example.
  • the extra-corporeal device 1502 may comprise a non- biocompatible coating. This coating may provide electrical isolation and/or protection to the device.
  • the shape of the coil for example a flat coil or a solenoid is not essential to implementing the invention. An effect of changing the coil may alter the direction of generated magnetic flux, requiring realignment of receiving and transmitting coils in order to effectively transfer power between an implantable rechargeable power supply and an extra-corporeal transmitting device.
  • sub-optimal alignment can be used in order to position the transmitting coil in a desired location.
  • the transmitting coil may be located in soft furnishings, or within a room etc.
  • the transmitting power of the transmitter may have to be increased to facilitate magnetic coupling with the receiver coil.
  • a resonant operating frequency of the transmitter and receiver may have to be modified.
  • An advantage of using sub-optimal alignment may be that the patient is not required to wear a garment incorporating one or more transmitting coils.
  • Embodiments discussed above may be utilised in any implantable device, whether subcutaneous or intravascular, for example, pacemakers, neural stimulators or heart pumps. It should be implied from the above description that the sizes of the elements disclosed above may be changed to suit the application.
  • References to DC/ AC converters and AC/DC converters may relate to any suitable device for carrying out aspects of the invention.
  • an AC/DC converter may comprise a rectifier network comprising a number of diodes.
  • a DC/ AC converter may comprise an inverter network comprising a number of semiconductor switches.
  • references to magnetic coupling, magnetic transmission/generation, or magnetic flux etc. can also be defined by the term 'inductive coupling'.

Abstract

La présente invention concerne une alimentation électrique rechargeable destinée à un dispositif médical intra-corporel, comprenant des moyens implantables de réception d'énergie électrique destinés à recevoir de l'énergie électrique sans fil et des moyens implantables de stockage d'énergie électrique. L'invention concerne également un dispositif médical intra-corporel comprenant lesdits moyen de réception d'énergie électrique et lesdits moyens de stockage d'énergie électrique, et un système et un procédé de transmission de l'énergie électrique à ladite alimentation électrique rechargeable.
PCT/EP2016/069159 2015-08-12 2016-08-11 Système, appareil et procédé de transfert de courant sans contact amélioré dans des dispositifs implantables WO2017025606A1 (fr)

Applications Claiming Priority (6)

Application Number Priority Date Filing Date Title
US14/825,054 US20170043077A1 (en) 2015-08-12 2015-08-12 System and method for contactless power transfer in implantable devices
US14/825,022 US20170047762A1 (en) 2015-08-12 2015-08-12 Apparatus for contactless power transfer in implantable devices
US14/825,054 2015-08-12
US14/825,022 2015-08-12
US14/923,256 US20170117739A1 (en) 2015-10-26 2015-10-26 System, apparatus and method for improved contactless power transfer in implantable devices
US14/923,256 2015-10-26

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WO2019036568A1 (fr) * 2017-08-18 2019-02-21 Cardiac Pacemakers, Inc. Dispositif médical implantable comprenant un concentrateur de flux et une bobine de réception disposée autour du concentrateur de flux
CN112584894A (zh) * 2018-08-31 2021-03-30 豪夫迈·罗氏有限公司 模块化植入式医疗装置
WO2021183599A1 (fr) * 2020-03-10 2021-09-16 Tc1 Llc Systèmes et procédés de transfert d'énergie sans fil pour dispositifs d'assistance ventriculaire
WO2021230921A1 (fr) * 2020-05-13 2021-11-18 Medtronic, Inc. Algorithme pour utiliser de multiples entrées afin de moduler le taux de charge d'un système entièrement implantable
EP4035728A1 (fr) * 2021-02-01 2022-08-03 Walter Mehnert Chargeur avec une suspension à cardan pour un stimulateur cardiaque
WO2022162238A1 (fr) * 2021-02-01 2022-08-04 Walter Mehnert Dispositif de charge

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EP4035728A1 (fr) * 2021-02-01 2022-08-03 Walter Mehnert Chargeur avec une suspension à cardan pour un stimulateur cardiaque
WO2022162238A1 (fr) * 2021-02-01 2022-08-04 Walter Mehnert Dispositif de charge

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