CHARGER

Description

[0001] The present invention relates to a charger for contactless charging of an energy storage device of an implant.

[0002] Patent document DE 10 2018 205 940 A1 discloses an electronic pacemaker that can be completely implanted into the body of a living being. This pacemaker includes an energy storage device that supplies the pacemaker's electronics with electrical energy and can be recharged wirelessly after discharge.

[0003] The energy storage device is recharged wirelessly via "indirect" induction using a magnetization section that responds to an alternating magnetic field in such a way that, once a certain magnetic field strength is reached, a wave of flipping domains (Weiss domains) appears within it. The occurrence of the wave is independent of the frequency of the alternating magnetic field, which only indicates how often the wave occurs per unit of time.

[0004] Due to the rapid change in magnetic flux, this wave causes a coil located in close proximity to emit a voltage pulse that charges the energy storage device.

[0005] A charger shown in the patent document generates the alternating magnetic field, wherein the charger is positioned on or near a surface of the organism's body during the charging process, and the alternating magnetic field is intended to trigger the magnetization section of the pacemaker in the manner described.

[0006] The charger contains a number of coils to generate the alternating magnetic field. The portion of the alternating magnetic field that penetrates the surface of the body and reaches the magnetization section is part of the weak stray field of the coils.

[0007] This stray field of the coils is extremely inhomogeneous and decreases sharply with increasing distance from the coil.

[0008] For this reason, recharging the energy storage device, depending on the implantation depth of the pacemaker, requires a meticulous adjustment of the electrical operating parameters of the aforementioned coils and a strong stray field with the corresponding direction of the field vector, so that the wave of flipping domains in the magnetization section is generated reliably and periodically.

[0009] If the magnetic field in the magnetization section deviates too much from a certain optimal value of field strength or flux density because it is too weak or too inhomogeneous, the wave necessary for charging will not be triggered.

[0010] In order to achieve the necessary field strength or flux density in the stray field, the known charger must have a very high current / voltage resistance design.

[0011] If one attempts to charge the energy storage device using ordinary (frequency-dependent) induction according to the transformer principle, one is exposed to even greater, negatively impacting effects in addition to the problems already explained, especially with regard to field strength / flux density.

[0012] Ideally, this type of charging would require the highest possible frequencies to achieve adequate energy transfer while maintaining an acceptable field strength / flux density. However, increasing the frequency also leads to a significant increase in opposing skin effects within the body's conductive tissue, such that the alternating magnetic field penetrates the body only minimally, making it impossible to reach the implant.

[0013] An alternative approach of increasing the field strength / flux density of the stray field at the location of the implant while simultaneously using a low frequency is also hardly possible, because the inductive AC resistances of coils located in the charger would have to be chosen so large that current and / or voltage values ​​would be in impractical ranges.

[0014] Further state of the art can be found in WO 2009 / 051539 A1, WO 2017 / 025606 A1 and US 2012 / 146575 A1.

[0015] Against this background, the object of the invention is to create a charger for the contactless charging of an implant's energy storage device, which allows for easier and more reliable generation of a magnetic alternating field necessary for charging.

[0016] Furthermore, the object of the invention is to create a charger that is simple compared to the state of the art, particularly with regard to current and voltage values.

[0017] These problems are solved with a charger according to claim 1. Preferred embodiments of the charger according to the invention are the subject of the dependent claims.

[0018] According to one aspect of the invention, the charger for contactless charging of an energy storage device of an implant that is implanted in the body of a living being includes the following features: at least one freestanding coil extending along a coil axis and configured to generate an alternating magnetic field; wherein When the charger is used as intended, the body is arranged spatially relative to the coil in such a way that the alternating magnetic field, which extends in the area inside the coil along the coil axis, penetrates the body to charge the energy storage device.

[0019] Strictly speaking, the charger's coil generates an alternating electromagnetic field. However, for the invention, only the magnetic component of the alternating electromagnetic field is relevant. Therefore, the present description refers only to an alternating magnetic field.

[0020] The implant, whose energy storage device is charged by the charger according to the invention, is, for example, a cardiac pacemaker, a brain pacemaker, an organ pacemaker, or an analysis unit. The latter analysis unit is, for example, designed to continuously or at specific intervals determine parameters such as blood pressure and / or blood values. Particularly preferred is the implant a cardiac pacemaker or pacemaker network that is located in or on the human heart, or implanted at these positions.

[0021] To become independent of the frequency of the alternating magnetic field, a key element of the implant is a magnetization section with aligned magnetic domains. A remagnetization wave, in the form of continuously reversing magnetic domains, propagates across this section when the amplitude (B-field) of the alternating magnetic field generated by the charger reaches a specific value within the magnetization section. The magnetization section can be, for example, a pulse wire or Wiegand wire.

[0022] A coil located in close proximity to the magnetization section generates a voltage pulse due to the remagnetization wave and the associated rapid change in magnetic flux. This pulse powers, for example, charging electronics and triggers a charging pulse. The energy storage device can then be charged with this charging pulse. The alternating magnetic field generated by the charger triggers the remagnetization wave with each polarity reversal, resulting in an equal number of charging pulses that charge the energy storage device.

[0023] Alternatively, the implant can be designed differently, such that its energy storage is charged using conventional, frequency-dependent induction. For this purpose, the implant has a receiving coil with a preferably specially shaped core, whereby the receiving coil emits charging pulses that depend on the frequency and magnitude of the generated alternating field. The receiving coil is wound around the core in a longitudinal direction.

[0024] The charger according to the invention is therefore intended for charging by utilizing "ordinary", frequency-dependent induction and / or "indirect", frequency-independent induction.

[0025] A pacemaker or pacemaker network which – using “indirect” induction for charging – has the magnetization section described above and whose energy storage is charged by generating the remagnetization wave, is known from patent documents DE 10 2019 124 435 and EP 3 756 726 A2.

[0026] The details contained in these patent documents regarding the respective charging pulse generation sections, in particular the magnetization sections including the coils wound around them and emitting the respective voltage pulse, as well as regarding the respective charging electronics, are incorporated by reference.

[0027] The frequency f of the alternating magnetic field generated by the charger according to the invention is in particular between 0.1 kHz ≤ f ≤ 10 kHz, especially at f = 2 kHz, 3 kHz, 4 kHz, or 5 kHz. The frequency f is preferably adapted to the spatial dimensions and material properties of the magnetization section and a related propagation time of the remagnetization wave passing over the magnetization section.

[0028] The frequencies are also suitable for charging the implant in its alternative version based on ordinary induction, provided that the receiving coil of the implant has the specially shaped core.

[0029] The shape of the freestanding coil of the charger according to the invention can vary. For example, the coil can be circular, rectangular, or square. The coil is designed to be freestanding and dimensionally stable, independent of the body of the living being. This means that the body can move relative to the dimensionally stable coil. Furthermore, the coil has such spatial dimensions that the body of the living being can move relative to the coil without any contact with the coil or its elements, such as frames or insulation, so that ultimately the body is completely without contact with the coil, and the implant is located within the area inside the coil or within the alternating magnetic field extending along the coil axis.

[0030] The coil of the charger according to the invention generates a nearly homogeneous alternating magnetic field in the area extending within the coil along the coil axis, wherein the amplitude of the corresponding magnetic flux density in an entire inner region of the coil radial with respect to the coil axis has such values ​​that i. assuming the magnetic field (direction of the B-vector) and the intended direction of travel of the remagnetization wave have the same orientation, each reversal of the alternating magnetic field triggers the remagnetization wave and thus the charging pulse, or ii. assuming the magnetic field (direction of the B-vector) and the intended orientation of the core of the receiving coil used for ordinary induction have the same orientation, each reversal of the alternating magnetic field results in the emission of the charging pulse.

[0031] Due to this field pattern, the exact positioning of the implant within the coil is not important, which makes a meticulous adjustment of the alternating field to the charging conditions, such as the depth of the implant, unnecessary.

[0032] Preferably, the charger is configured to rotate a vector of the alternating magnetic field for charging purposes, at least in two or three dimensions. In this respect, the charger is preferably configured to rotate the vector of the alternating magnetic field for charging without changing the corresponding amplitude of the vector. The rotation is achieved mechanically, as will be described below, for example, with reference to a suspension, or by changing superimposed individual alternating magnetic fields, which are located, for example, between sub-coils, as will be explained below.

[0033] Preferably, when the charger is used as intended, the body is arranged (without contact) relative to the freestanding coil such that a longitudinal axis of the body runs in the direction of the coil axis and is located inside the coil, with the alternating magnetic field reaching the location of the implant.

[0034] In this preferred embodiment of the charger, the longitudinal axis of the living being, particularly a human, runs in the direction of the coil axis. This embodiment is particularly advantageous when the orientation of the intended direction of travel of the remagnetization shaft running over the magnetization section, or the orientation of the core used for ordinary induction, coincides with the direction of the body's longitudinal axis. This condition can preferably be achieved by designing the implant such that its shape or anchoring mechanisms result in this orientation.

[0035] Preferably, the charger according to the invention further includes: a suspension which holds the coil and is configured to pivot the coil relative to the body about at least one, preferably two axes to rotate the vector, wherein the charger is preferably configured, for example, by a control unit, to control the suspension in order to pivot the coil into a certain orientation relative to the body to optimize the charging of the energy storage device.

[0036] Alternatively, the charger can be preferably configured to control a display device to show an operator in which direction to manually swivel the coil relative to the body to optimize the charging of the energy storage device.

[0037] If the intended direction of rotation of the remagnetizing wave or the orientation of the core used for ordinary induction does not coincide with the direction of the vector of the alternating magnetic field, excessive deviations can lead to a decrease in the charging pulse because the component of the magnetic field in the direction of the axis of the magnetizing section or the core becomes too small.

[0038] To allow for adjustment or adaptation of the direction of rotation of the remagnetizing shaft or core to the field alignment, or vice versa, a suspension is provided. The suspension is, for example, a gimbal suspension that allows the charger's control unit to pivot the charger's coil relative to the organism's body around two axes. This enables the alignment (vector of the magnetic field) of the alternating magnetic field generated by the coil to match the intended direction of rotation of the remagnetizing shaft or core. Alternatively, the gimbal suspension can be manually adjustable, with the indicator device preferably showing the corresponding direction.

[0039] Advantageously, swiveling the coil does not change the amplitude of the magnetic flux density, but only changes the orientation of the alternating magnetic field.

[0040] Furthermore, the suspension which holds the freestanding coil is movable relative to the body and / or a body support for holding the body is movable relative to the coil, wherebythe charger is set up, the suspension and / or to reposition the body mount to bring the freestanding coil into a specific position relative to the body to optimize the charging of the energy storage device.

[0041] For example, the charger includes a linear guide along which the entire coil suspension can be moved, preferably along the longitudinal axis of the body. The user can move the suspension along the linear guide either manually or automatically by entering appropriate instructions via a user interface on the control unit. The movement of the freestanding coil (and / or the aforementioned pivoting) is performed in such a way that the body of the living being, especially a human, does not touch any other elements of the charger, such as the coil or its components, except for the body support.

[0042] The charger is preferably configured to check whether, or to what extent, the orientation of the direction of rotation of the remagnetizing shaft or the core used for ordinary induction corresponds to the orientation of the magnetic field. For example, the charger is able to wirelessly query the state of charge of the energy storage device at specific intervals and to draw a conclusion about the charging efficiency based on the change in the state of charge of the energy storage device, the reversal frequency, and a known maximum amplitude of the charging pulses.

[0043] Preferably, however, the charger has a receiving unit configured to receive a quality signal emitted by the implant that reflects the charging efficiency, and the charger is configured to swivel the coil into a specific orientation to optimize charging, depending on the quality signal. / or to bring it into a specific position.

[0044] The quality signal can, for example, be a low-frequency signal that penetrates the human body and, if no antenna is provided for this purpose, the casing or housing of the pacemaker. The quality of the charging pulse is preferably proportional to the value of the integral ( ∫ i dt).With good charging pulses, i.e., with very high quality, the value can be up to 1000nC, for example. The signal indicating the quality can be, for example, the value of the integral of the charging pulse current over time ( ∫ i dt), i.e., its charge content. Alternatively, the quality signal can indicate the following ratio: (charge content of the emitted charge pulse / maximum possible charge content).

[0045] Alternatively, the quality signal can be a binary signal that enters an OK state when the charging pulse exceeds a certain threshold.

[0046] The control unit, monitoring the quality signal, controls the suspension, for example, the gimbal suspension, and determines an optimal coil position from various coil positions and the corresponding quality signals, into which the control unit then pivots the coil. In the described alternative, the charger can display directions on the indicator device in which the operator should pivot the coil.

[0047] The following are preferred parameters of the charger according to the invention and / or its coil: The magnetic flux density of the alternating magnetic field along the coil axis preferably has a value B in the mT range, preferably larger. / equal to 1mT, especially in the following areas: 1.0mT <= B <= 20.0mT, in particular 2.0mT <= B <= 20.0mT, 2.5mT <= B <= 8.0mT, 3.5mT <= B <= 7.0mT, 4.5mT <= B <= 6.0mT, 4.8mT <= B <= 5.2mT, or 5.0mT = B.

[0048] The coil has a diameter D such that the body of a living being, particularly a human, can be moved into the alternating magnetic field extending along the coil's axis within the coil without touching the coil or its components, and is positioned there without contact relative to the coil for charging purposes. The diameter is preferably in the following range: 0.6 m <= D <= 0.9m, 0.65m < = D <= 0.85m, 0.68m <= D <= 0.8m, or 0.72m = D; and / or The length of the coil preferably has a value I, where preferably 0.15m <= I <= 0.5m, 0.2m <= I <= 0.45m, 0.25m <= I <= 0.4m, or 0.33m = I.

[0049] The charger coil can be a continuously wound coil, especially if the longitudinal axis of the human body is intended to coincide with the coil axis.

[0050] Alternatively, the coil can be separated and constructed from two partial coils. The dimensions of the partial coils and their distance from each other are preferably chosen such that the separated coil behaves like a continuously wound coil, at least in a region radial to the coil axis. An example of a separated coil is a Helmholtz coil. By design, the human body is positioned between the partial coils and the magnetic field or alternating magnetic field located there, with the body's longitudinal axis running perpendicular to the coil axis.

[0051] The extended coil can also be held in place by an adjustable suspension.

[0052] Alternatively, the charger can also include two or three separated coils, the coil axes of which are preferably arranged in two or three spatial coordinates. When the charger is used as intended, the human body and the implant are located between the respective sub-coils, whereby the alternating magnetic fields generated by the separated coils, each located within a specific area of ​​its respective coil, superimpose between the sub-coils and reach the implanted device.

[0053] A targeted alignment of the magnetic alternating field resulting from the superimposed alternating fields can be achieved by differently controlling the phases and / or amplitudes of the respective coil pairs in order to optimize charging.

[0054] The control of the resulting alternating field can, for example, be based on the quality signal.

[0055] As can be seen from the second preferred embodiment and the third preferred embodiment of the charger described below, the previously mentioned, separated coils are freestanding, i.e., the respective partial coils arranged at a distance from each other are dimensionally stable and freestanding, so that the body of the living being (human being) can be moved into the alternating magnetic field and remain there for charging without contact with the coil or its elements.

[0056] Preferred embodiments of the charger according to the invention are explained below with reference to the accompanying figures. Figures 1A and 1BThe figures show a first preferred embodiment of the charger according to the invention, firstly in a perspective view and secondly in a view along a Z-axis shown in the figures, wherein the charger includes a coil which is held by a gimbal suspension. Figure 1C shows simulation results of the alternating magnetic field generated by the coil of the charger of the first preferred embodiment of the invention. Figure 1D shows the amplitude of the alternating magnetic field (B-field in mT) at the center of the coil radial to the coil axis. Figure 2A and 2B Figure 1 shows a second preferred embodiment of the charger according to the invention, which includes a coil consisting of a coil pair made up of two partial coils, wherein a suspension holds both partial coils and is configured to pivot and / or move the partial coils together. Figure 3A third preferred embodiment of the charger according to the invention is shown, comprising three coils, each of which is made up of two sub-coils, wherein the respective coil axes are spatially perpendicular to each other and in a superposition area located between the respective coils, the amplitude and vector of the alternating magnetic field can be adjusted by controlling the coils.

[0057] The embodiments of the charger according to the invention, described below, serve to charge an energy storage device of an implant that is completely implanted in a human or animal body.

[0058] The implant is generally an entity that performs certain functions in the implanted state and for this purpose has at least electronics and the aforementioned energy storage device that supplies the electronics.

[0059] Preferably, the implant may also include electrodes for recording body data (body information) and / or delivering impulses to the body, and preferably a communication unit that acts as an interface to the outside world.

[0060] The implant is, for example, a cardiac pacemaker, brain pacemaker, bladder pacemaker and / or an analysis unit that records bodily data such as blood pressure and / or blood values.

[0061] The implant has a feature for contactless recharging of the energy storage device. i. a charging pulse generation section with charging electronics, such as those described, for example, in patent document DE 10 2019 124 435; and / or ii. a receiving coil wound around a preferably specially shaped core, wherein the receiving coil with core enables charging of the energy storage device based on ordinary induction.

[0062] An essential element of the charging pulse generation section is a magnetization section, for example a Wiegand wire, with aligned magnetic domains which can be influenced by the magnetic field component in its axial direction of an alternating electromagnetic field generated by the embodiments of the charger according to the invention, such that a remagnetization wave in the form of domino-like flipping domains (Weisse domains) runs over the magnetization section.

[0063] The remagnetization wave leads to such a high rate of change of magnetic flux that a coil located in close proximity to the magnetization section generates a voltage pulse that leads to a charging pulse of the energy storage device.

[0064] This type of recharging of the energy storage device is particularly advantageous in that the frequency of the alternating magnetic field can be reduced to such an extent that no adverse effects, such as skin effects, prevent the alternating magnetic field from penetrating the body and reaching the magnetization section.

[0065] For example, the magnetization section can be a Wiegand wire around which a coil is wound.

[0066] The speed of the remagnetization wave traveling along the Wiegand wire is approximately 800 m / s when idling, with the length of the Wiegand wire within the pacemaker ranging from 0.7 to 1.2 cm. This results in a idling time of the remagnetization wave (wave of flipping domains) on the order of 10–20 µs.

[0067] Taking these values ​​into account, the charger according to the invention, which will be explained below, generates the alternating magnetic field with a frequency in the range of 0.1 to 10 kHz. In this frequency range, the alternating magnetic field penetrates very deep into the body of the living being and can thus easily reach the magnetization section of the implant for contactless charging.

[0068] The aforementioned frequency range is also suitable for charging via ordinary induction, at least if the aforementioned core runs through the coil.

[0069] The embodiments of the charger according to the invention are explained below under the assumption that the implant is a pacemaker that is completely implanted in / on the human heart. However, the invention is not limited to this.

[0070] The pacemaker has a housing that encapsulates the energy storage device and the corresponding electronics. The pacemaker housing has a volume on the order of 1 cm³.

[0071] Necessary electrodes of the pacemaker lie exposed on the surface of the casing and touch sections of the human heart, and / or are designed as anchoring electrodes that are anchored in the human heart and hold the pacemaker in place.

[0072] The pacemaker receives body data via the electrodes, i.e., information about the activity of the heart, and / or can use this information to deliver stimulation impulses to the heart.

[0073] The energy storage device of a pacemaker, for example, is an electrochemical energy storage device, specifically a rechargeable battery, such as a lithium-ion battery, with a capacity sufficient to supply all electronic components of the pacemaker with electrical energy for a period of, for example, 0.75 to 1.25 years. If it is recharged, for example, every 0.5 years, the energy supply to all electronic components is thus ensured.

[0074] Charging is done contactlessly using ordinary or indirect induction via the charger described in more detail below. (First embodiment)

[0075] With reference to Figures 1A to 1E A first preferred embodiment of the charger according to the invention is explained below.

[0076] The charger 100 according to the first preferred embodiment includes a freestanding (dimensionally stable) coil 110 that generates the alternating magnetic field necessary for charging. The coil 110 has such spatial dimensions that a body holder 120 of the charger 100, intended for a patient P, can be partially accommodated within the coil 110 without coming into contact with the freestanding coil 110 or its elements, such as insulation, frame, windings, etc.

[0077] In the preferred embodiment of the charger 100, the body support 120 is a couch on which the patient P lies or is arranged when the charger 100 is used as intended.

[0078] Patient P is the carrier of a schematically indicated pacemaker I, which is completely implanted in the heart of patient P.

[0079] The body support 120 runs in the direction of a Figures 1A and 1BThe Z-axis shown passes through coil 110. The Z-axis corresponds to a coil axis of coil 110. When the patient P lies on the body support 120, as described below, a body axis of the patient runs in the direction of the coil axis of coil 110, whereby the alternating magnetic field located in the area inside coil 110 penetrates the body of the patient P and reaches the pacemaker I to charge the energy storage device.

[0080] In the preferred embodiment, the coil 110 is a circular coil with a diameter D, wherein a corresponding coil plane is located in the Figures 1A and 1B The XY plane shown is perpendicular to the coil axis (Z-axis).

[0081] Alternatively, the coil 110 can also be a square or rectangular frame coil. In the first preferred embodiment, the diameter D is 0.72 m, but can vary as long as the patient can position themselves within the coil without touching it.

[0082] The coil 110, for example, has a single-layer winding with a plurality of turns w, formed from an electrical conductor, for example a copper conductor. In the first preferred embodiment, the number of turns w = 10, although this value is merely preferred and can also vary.

[0083] The electrical conductor forming the winding preferably has a rectangular cross-section of 320 mm², resulting from a side length of 32 mm pointing in the direction of the Z-axis and a side length of 10 mm perpendicular to it. In addition, the surface of the electrical conductor is covered with electrical insulation with a thickness of 0.5 mm.

[0084] This results in a length I of the coil 110 in the direction of its coil axis (Z-axis) of 0.32 m without taking the insulation into account or of 0.33 m taking the insulation into account, whereby for the first preferred embodiment the condition D > I applies.

[0085] In this configuration of coil 110, the inductance L has a value of 87 µH. The invention is not limited to the described configuration and the parameters mentioned. In general, it is preferred that the configuration of coil 110 is designed such that the inductance lies within the following range: 0.02 mH ≤ L ≤ 0.3 mH.

[0086] The coil 110 of the charger 100 according to the invention is preferably operated during the charging of the energy storage of the pacemaker I in such a way that it generates in its interior the alternating magnetic field with an amplitude (magnetic flux density B) in the range of greater than or equal to 1mT, preferably in the range of 2.5mT <= B <= 8.0mT, in particular in a range of 5mT.

[0087] The alternating magnetic field with these values ​​of magnetic flux density B is located in the area inside the coil 110 and runs along the coil axis of the coil 110.

[0088] The magnetization section contained in the pacemaker I, which is preferably the aforementioned Wiegand wire, exhibits reliable behavior at the aforementioned values ​​of magnetic flux density B and a frequency f (reversal frequency) of the alternating magnetic field in the aforementioned range of 0.1 to 10 kHz, particularly at 2 kHz, such that each reversal of the alternating magnetic field is very likely to trigger the remagnetization wave and thus lead to the charging pulse of the energy storage device.

[0089] The energy storage device can also be charged by ordinary induction in this frequency range, especially at frequencies above 2kHz, if the pacemaker's receiving coil has the appropriate core.

[0090] The described construction of the charger 100 according to the invention in the first preferred embodiment is particularly advantageous because electrical operating parameters are in orders of magnitude that allow the trouble-free operation of the charger 100 in an ordinary medical practice.

[0091] The magnetic flux density B of the alternating magnetic field generated by coil 110 is given by the following relationship: B = μ 0 * I * w / D

[0092] The charger 100 according to the invention preferably generates an alternating electric current with a strength of I = 300 A in the winding of the coil 110. With the aforementioned w = 10 turns, the preceding equation (1) yields a magnetic flux density B of 5.25 mT, which is sufficient for the reliable triggering of the Wiegand wire or magnetizing section, or for sufficient ordinary induction in the aforementioned ranges.

[0093] Taking into account the AC resistance of the coil 110, which results from ω*L, with ω=2πf, an AC voltage necessary for the generation of the alternating current I follows from U=I*ω*L and is therefore 327 V at a frequency f of 2 kHz of the magnetic alternating field.

[0094] Both the value of the alternating current I generated in the winding and the corresponding voltage U are within the range that can be provided in normal buildings / medical practices. Therefore, the charger 100 according to the invention does not necessarily need to be installed in a separate facility, as is the case, for example, for the operation of an MRI scanner.

[0095] This is advantageously achieved by the fact that the coil 110 of the charger 100 according to the invention is part of a resonant circuit, for example a parallel resonant circuit. In this way, only the active power (copper losses) needs to be drawn from the mains.

[0096] Figure 1B Figure 1 schematically shows an amplifier 151 and a capacitor 152, which are together contained in a control unit 150 of the charger 100. The capacitor 152, together with the coil 110, forms the aforementioned parallel resonant circuit.

[0097] The parallel resonant circuit is dimensioned such that it is in resonance during normal operation of the charger 100. Taking into account the inductance of L = 87 µH of the coil 110, the relationship 1 / (ω*C) = ω*L, which applies in the resonance case, results in a capacitor capacitance of C = 72.8 µF.

[0098] The ohmic resistance R of the coil 110 is essentially determined by the material and dimensions of the electrical conductor forming the winding. In the present first preferred embodiment of the charger 100 according to the invention, the ohmic resistance R of the electrical conductor of the coil 110 is approximately 1.24 mΩ.

[0099] This results in an active power consumption of 56 W for coil 110 in the example, assuming a corresponding RMS value Ieff of the alternating current flowing through coil 110. This active power consumption of the parallel resonant circuit can easily be supplied by a standard building power supply (e.g., 230 V; 50 Hz). This means that the charger 100 according to the invention can be connected to a standard wall socket via the control unit 150. Figures 1A and 1B The diagram shows a schematic of such a connecting cable.

[0100] When the energy storage of the pacemaker I needs to be recharged in its implanted state, the patient P lies down, as is evident from Figures 1A and 1B It is evident that the lounger is 120.

[0101] A spatial position of the patient P or the couch 120 relative to the coil 110, with respect to the Z-direction (positive or negative direction of the Z-axis), is achieved by the control unit 150 of the charger 100 displacing a suspension 140 of the coil 110, which will be explained below, relative to the couch 120 / patient P. The suspension 140 holds the dimensionally stable coil 110 so that it is freestanding. For this purpose, the charger 100 has a linear guide 130, which is arranged below the couch 120 and which holds the suspension 140 of the coil 110 so that it can be displaced in the Z-direction.

[0102] The control unit 150 is configured to actuate the linear guide 130 in order to move the suspension 140 to a specific position in the Z-direction. Alternatively / additionally, the body support / bed 120 can be mounted in a movable position, so that the control unit 150 of the charger 100 can move the body support / bed 120 relative to the coil 110 for contactless positioning of the patient P.

[0103] When charged as intended, patient P and coil 110 have such a spatial relationship to each other that the pacemaker I is located in the area along the coil axis inside coil 110.

[0104] This condition is in Figures 1A and 1BThe pacemaker I is located within the cylinder volume V defined by coil 110, which is calculated as (D / 2) 2< *π*l. The alternating magnetic field running along the coil axis in this area penetrates the patient P's body and reaches the pacemaker I.

[0105] The magnetic flux density B has values ​​adequate for charging throughout the entire cylinder volume, which is why the specific position of the pacemaker I within the cylinder volume V plays a subordinate role, as long as the orientation of the magnetizing section or the core used for ordinary induction is correct. This will be explained in the following sections. Figures 1C to 1E evident.

[0106] Figures 1C and 1Dshow the strength and orientation of the magnetic flux density B of the alternating magnetic field generated by the coil 110 when the alternating current of I = 300 A flows through the winding of the coil 110. Figure 1C corresponds to a sectional view of coil 110, where the sectioning plane is in Figures 1A and 1B The ZX plane shown corresponds to this and contains the center point of coil 110. The center point of coil 110 is simultaneously the origin of the waveform shown in the diagram. Figures 1A and 1B shown coordinate system.

[0107] Figure 1D In this context, the amplitude of the magnetic flux density B is shown and Figure 1C the corresponding vector representation, where the figures represent the quantities resulting in space.

[0108] The Figure 1DThis makes it clear that the amplitude of the magnetic flux density B within the coil 110, particularly in the region of the middle plane (XY plane, with Z = 0), has an amplitude above 4.5 mT across the entire diameter D (see regions in Figure 1D In addition, what Figure 1C This clarifies that the orientation (vector) of the magnetic flux density B in the region of the middle plane is essentially homogeneous, i.e., the vectors indicating the orientation of the magnetic flux density B run parallel to the coil axis.

[0109] Figure 1DThis shows in detail how the amplitude of the resulting magnetic flux density B in the middle plane of coil 110 (Z = 0) changes radially (X and / or Y direction) from the coil axis or the origin of the coordinate system. The magnetic flux density B has a resultant magnetic flux density of 4.5 mT at (X, Y, Z) = (0, 0, 0) and increases radially to approximately 8 mT.

[0110] According to its intended use, the charger 100 of the first preferred embodiment is operated such that the pacemaker I is located in the cylinder volume V defined by the coil 110 when the corresponding energy storage device is being charged. However, it is particularly preferred that, during the intended operation of the charger 100 according to the invention, the patient P is positioned relative to the coil 110 such that the pacemaker I is located at a point in the central (X / Y) plane of the coil 110.

[0111] The magnetization section, in particular the Wiegand wire, or the core of the pacemaker I, is oriented during the intended operation of the charger 100 such that the intended direction of rotation of the remagnetization shaft, or a longitudinal extension of the core, coincides with the direction of the coil axis / Z-axis and thus with the main component (Z-component) of the resulting magnetic flux density B. The intended direction of rotation corresponds to the direction in which the remagnetization shaft should travel across the magnetization section to achieve optimal voltage pulses or charging pulses. For the aforementioned Wiegand wire, this direction of rotation generally corresponds to its longitudinal axis.

[0112] The alignment of the magnetization section / direction of rotation of the remagnetization wave or the longitudinal extent of the core used for ordinary induction with the direction of the coil axis is achieved by ensuring proper orientation during implantation of the pacemaker I or the magnetization section it contains. For example, the pacemaker I has electrodes and / or anchors designed in such a way that the alignment of the magnetization section / longitudinal extent of the core used for ordinary induction with the body axis (and thus with the Z-axis / coil axis) is automatically achieved during implantation.

[0113] The alignment of the magnetization section, in particular the alignment of the longitudinal extent of the Wiegand wire, or the longitudinal extent of the core used for ordinary induction in the direction of the Z-axis / coil axis, ensures that every reversal of the electromagnetic alternating field reliably triggers the remagnetization wave / ordinary induction, resulting in a desired voltage pulse, which in turn leads to the charging pulse for the energy storage device.

[0114] The explanations regarding the alternating magnetic field generated by coil 110 reveal that the reliable triggering of the remagnetization wave or the reliable induction is independent of the location of the pacemaker or the magnetization section within the cylindrical volume V defined by coil 110. This is because a sufficiently homogeneous amplitude of the magnetic flux density B exists within coil 110, while the B-vector is simultaneously aligned along the coil axis (independent of location).

[0115] Therefore, meticulous adjustment and adaptation of the strength and orientation of the alternating magnetic field to the position and location of the pacemaker is not necessary.

[0116] Even if the pacemaker I has been implanted in the body of patient P in such a way that the direction of travel of the remagnetizing wave or the longitudinal extension of the core points in the direction of the patient's body axis, deviations may occur between the longitudinal extension of the core or the orientation of the magnetizing section and thus the direction of travel on the one hand and the coil axis on the other hand during the intended operation of the charger 100.

[0117] One reason for this could be the patient's individual physiological characteristics, which could lead to a different position of the pacemaker type I within the patient's body. Another reason could be simple physical movements by the patient during the charging process.

[0118] To bring and / or maintain the charging of the energy storage device in an optimal state, the suspension 140 is designed to be adjustable.

[0119] Firstly, the coil 110 can be moved in the direction of the Z-axis or coil axis by the linear guide 130.

[0120] Secondly, the suspension 140 is designed as a gimbal suspension. This allows the coil 110 to pivot around the respective position in Fi. guren 1A and 1B X-axis and Y-axis shown.

[0121] The control unit 150 is set up to use the aforementioned settings to optimize the charging of the energy storage device.

[0122] Optimizing the charging process requires determining the extent to which reversing the polarity of the alternating magnetic field results in the desired, sufficiently high charging pulses. If the orientation of the intended direction of rotation of the remagnetization shaft or the longitudinal extent of the core deviates too much from the coil axis, the generated voltage pulses will decrease in amplitude to such an extent that sufficient charging pulses for the energy storage device can no longer be achieved.

[0123] The pacemaker I preferably generates a quality signal Q as feedback, reflecting the efficiency of the charging process. This quality signal can be actively transmitted or passively monitored.

[0124] The transmitted quality signal Q can, for example, be a low-frequency signal that penetrates the body of the patient P and, if no external antenna is provided for this purpose, the casing or housing of the pacemaker.

[0125] The quality signal can be queried, for example, by having the pacemaker dampen defined frequencies.

[0126] The quality of the charging pulse is proportional to the value of the integral ( ∫ i dt). For good charging pulses, i.e., with very high quality, the value is, for example, up to 1000 nC. The signal Q indicating the quality can, for example, be the value of the integral of the current of the charging pulse over time ( ∫ i dt), i.e., specify its charge content.

[0127] The electronics of pacemaker I can be configured to transmit the quality-indicating signal Q for each charging pulse, or alternatively, only for those charging pulses that occur consecutively at specific intervals. These intervals are, for example, 25, 50, 100, 200, 500, 750, or 1000 charging pulses. It is also possible to transmit a value that corresponds to the average of all charging pulses occurring within a given interval. This reduces the energy required for active data transmission.

[0128] The control unit 150 has a receiver and is configured to evaluate the quality signal Q from the pacemaker I. Based on the quality signal Q, the control unit 150 performs appropriate steps to optimize charging by pivoting the coil 110 around the X / Y axes and / or moving it in the Z direction until the quality signal indicates optimal alignment.

[0129] Preferably, the quality signal Q is proportional to the charging efficiency.

[0130] The signal Q indicating the quality of the charging pulse can alternatively be, for example, a binary signal that is in an OK state when the charging pulse, or its charge content, exceeds a threshold, and in an NG state when the charging pulse does not exceed the threshold. The threshold can be, for example, 50%, 55%, 60%, 65%, 70%, 75%, 80%, 85%, or 90% of the charge content available through the magnetization section.

[0131] If the quality signal Q is a binary signal, the threshold for the OK state of the signal is preferably in higher ranges, because the threshold serves as a criterion for ending the pivoting of coil 110 around the respective axes and for evaluating the achieved position of the coil as optimal. For this purpose, for example, the extreme positions (change from good to bad or vice versa) are evaluated.

[0132] In general, the charger 100 according to the invention can also be used with implants that do not emit a quality signal Q, but merely have the functionality that the control unit 150 can query the state of charge of the energy storage device. For the application shown, for example, the corresponding electronics of the pacemaker I can be designed such that the state of charge of the corresponding energy storage device can be queried via a transmit and receive function of the pacemaker I.

[0133] This allows the control unit 150, as an alternative to the signal Q indicating the charging quality, to infer the charging efficiency from repeated queries of the energy storage device's state of charge during charging. Specifically, the control unit 150 can infer the quality / efficiency of individual charging pulses from information about changes in the state of charge, the time interval between queries, a known maximum amplitude of the charging pulses, and the polarity reversal frequency. The time interval at which the control unit 150 queries the energy storage device's state of charge is preferably 0.5 min, 1.0 min, 1.5 min, 2.0 min, 2.5 min, 3.0 min, 3.5 min, 4.0 min, 4.5 min, 5.0 min.

[0134] Once the control unit 150 has determined the quality of the charging pulses, it activates the gimbal suspension 140 to pivot the coil 110 around the respective axes (X-axis and / or Y-axis) and / or to move it along the Z-axis to optimize charging. This pivoting and / or moving is performed in such a way that the patient does not come into contact with the freestanding (rigid) coil or its components (contactless). (Second embodiment)

[0135] A second preferred embodiment of the invention is described below with reference to Figures 2A and 2B explained.

[0136] Figure 2A shows the construction of a charger 200 according to the second preferred embodiment of the invention as seen in the direction of the Z-axis and Figure 2B a perspective view.

[0137] The charger 200 is used to charge an energy storage device of a pacemaker I, which is identical in construction to the one described with reference to the first embodiment. In this respect, reference is made to the descriptions of the first embodiment regarding the construction and functionality of the pacemaker I.

[0138] The charger 200 includes a freestanding coil 210, which is configured to generate the alternating magnetic field required for the indirect charging of the energy storage device. The coil axis A of the coil 210 runs in Figure 2A in the direction of the Y-axis of the coordinate system shown there.

[0139] In contrast to the first preferred embodiment, the winding of the coil 210 is not continuous, but preferably in the middle of the coil 210, which simultaneously corresponds to the origin of the coordinate system, is pulled apart in such a way that the coil 210 is made up of partial coils.

[0140] The coil comprises two circular sub-coils 211 and 212, which are arranged axially to each other and have the same diameter D. The sub-coils 211 and 212 are arranged at a distance R1 from each other and have the same winding direction.

[0141] The winding of coil 210 runs over a connecting arm 213 and thus connects parts of the winding that form the sub-coils 211 and 212. In this embodiment, the connecting arm 213 is a closed ring, preferably circular.

[0142] The winding is, as in the first preferred embodiment, single-layered, and the sections of the winding forming the partial coils necessarily have the same winding direction.

[0143] In the present embodiment, the electrical conductor forming the partial coils 211, 212 preferably has the same cross-sectional dimensions as in the first preferred embodiment; rectangular with a side length of 32 mm in the direction of the coil axis and a side length of 10 mm in the radial direction to the coil axis. A section of the electrical conductor running over the connecting arm 213 may have the aforementioned cross-sectional dimensions or be dimensioned differently.

[0144] Each of the sub-coils 211 and 212, for example, has a diameter of 160 cm and five turns (w = 5). The distance R1 between the sub-coils 211 and 212 preferably corresponds to the radius of the sub-coils, i.e., 80 cm in the present embodiment, or is preferably smaller than the radius. The diameter D of the sub-coils 211 and 212 can be larger if a greater distance R1 between the sub-coils is required.

[0145] A suspension 240 holds the dimensionally stable coil 210 so that it is freestanding by adjustingly supporting the ring 213 forming the connecting arm 213, the suspension 240 having adjustment mechanisms for this purpose.

[0146] The adjustment mechanisms include a rotary bearing 241, which allows the connecting arm 213 and thus the coil 210 to be moved in the Fig. 2A and 2B The adjustment mechanisms have ball bearings 242, which allow the connecting arm / ring 213, which is connected to a bearing ring 243 via the rotary bearing 241, to be pivoted or rotated about the X-axis of the coordinate system shown. Figure 2A and 2B to pivot or rotate the Z-axis shown. As can be understood from this, the connecting arm / ring 213 can be rotated by the ball bearings 242 supporting the bearing ring 243 so far (90 degrees) that the rotary bearing 241 is not the one shown. Figure 2A and2B The X-axis shown corresponds to the Y-axis shown.

[0147] The adjustment mechanisms (rotary bearing 241, ball bearing 242) allow the coil 210 to be aligned in a desired orientation relative to the implanted pacemaker I.

[0148] Additionally, the charger 200 of the second preferred embodiment of the invention can include the linear guide 130, which has already been described with reference to the first preferred embodiment. Reference is made to the corresponding descriptions in the context of the first preferred embodiment. As in the first preferred embodiment, the couch 220 can preferably be displaceable in the Z-direction. If this is the case, the linear guide 130 is preferably not present.

[0149] A control unit 250, configured to perform the functions described with reference to the first preferred embodiment, is electrically connected to both the suspension 240 and the coil 210. The coil 210, as in the first preferred embodiment, is part of a Figure 2A parallel resonant circuit not shown, wherein the corresponding other elements of the resonant circuit, such as the amplifier and capacitor already mentioned, are included in the control unit 250.

[0150] A body support 220, which, as in the first preferred embodiment, is a couch, runs between the partial coils 211 and 212 perpendicular to the drawing plane of the Figure 2A in the direction of the Z-axis.

[0151] When the energy storage of patient P's pacemaker I needs to be recharged, patient P lies down on bed 220 and is positioned between subcoils 211 and 212. Patient P's body axis, or longitudinal axis, extends in the same direction as bed 220 along the Z-axis shown. Patient P is in Figure 2A shown schematically.

[0152] The coil 210 generates a uniform alternating electromagnetic field, even though the winding is not continuous but is separated into sub-coils 211 and 212. Put another way, due to the configurations, dimensions, and spatial relationship to each other described above, both sub-coils 211 and 212 act like a single coil with a continuous winding. In the present second embodiment, the coil 210 preferably has the structure of a so-called Helmholtz coil.

[0153] Both sub-coils 211 and 212 each generate a part of the total resulting alternating magnetic field, with the magnetic field extending within coil 210 along the coil axis A passing through interior spaces of sub-coils 211, 212 and the area between sub-coils 211, 212.

[0154] The area between the sub-coils is a superposition area in which the parts of the alternating magnetic field generated by the sub-coils superimpose in such a way that the resulting alternating magnetic field extends along the coil axis A.

[0155] The orientation-determining vectors of the alternating magnetic field, which passes through the interiors of the sub-coils 211, 212 and the superposition region located between the sub-coils, show parallel paths. Furthermore, under the same assumptions / operating parameters as shown for the first embodiment, the magnetic flux density B in the superposition region has values ​​that are above 4 mT over considerable distances.

[0156] These values ​​are sufficient to initiate the described remagnetization wave, which runs across the magnetization section or Wiegand wire of pacemaker I and leads to the charging pulse of the energy storage device, or the ordinary induction leading to the charging pulse.

[0157] In contrast to the first preferred embodiment, the alternating magnetic field located inside the coil along the coil axis A does not penetrate the body of the patient P parallel to its body axis running in the Z direction, but perpendicular to it.

[0158] The charger 200 is therefore specifically designed for use in cases where the pacemaker I is oriented in the body of the patient P in such a way that the intended direction of travel of the remagnetization wave of the magnetization section or the longitudinal extension of the core does not point in the direction of the body axis (Z direction), but deviates significantly from it and runs essentially in the Y and / or X direction.

[0159] The adjustment of an optimal position and orientation of the coil 210 in relation to the body of the patient P proceeds similarly to the first preferred embodiment of the charger according to the invention, in that the control unit 250 controls the adjustment mechanisms and / or the linear guide 130 and adjusts and aligns the coil 210 relative to the patient / pacemaker I in a manner that is contactless until optimal charging takes place. (Third embodiment)

[0160] Figure 3 Figure 3 shows a third preferred embodiment of a charger 300 according to the invention. The charger 300 also serves to charge an energy storage device of an implant I, such as the pacemaker I described above.

[0161] Regarding the structure and functionalities of the pacemaker I, reference is made to the descriptions of the first and second embodiments.

[0162] The charger 300 generates the alternating magnetic field necessary for charging the energy storage device in a similar manner to the coil 210 of the charger 200 according to the second preferred embodiment, but makes a suspension for changing the spatial orientation of the alternating magnetic field unnecessary.

[0163] For this purpose, the charger 300 has a first coil, a second coil and a third coil, which are arranged together in a freestanding and dimensionally stable manner.

[0164] The first coil includes a first coil pair, which consists of a first partial coil 311 and a second partial coil 312, with the corresponding coil axis A pointing in the direction of the Figure 3 The Y-axis of the corresponding coordinate system shown runs along or corresponds to it.

[0165] The second coil contains a second coil pair, which is similarly composed of a first partial coil 221 and a second partial coil 222. The coil axis B of the second coil corresponds to that in Figure 3 X-axis of the corresponding coordinate system shown.

[0166] Ultimately, the charger 300 includes a third coil, which in turn is composed of a first sub-coil 331 and a second sub-coil 332. The coil axis C of the third coil corresponds to the Z-axis of the one in Figure 3 shown coordinate system.

[0167] All coil axes are preferably spatially perpendicular to each other.

[0168] In contrast to the previous embodiments, the coils or sub-coils are not circular, but designed as frame coils with rectangular coil planes.

[0169] All sub-coils, each forming the coil pairs, preferably have the same construction with regard to the electrical conductor forming the respective winding and the number of turns w, and each has the same winding direction. The dimensions of the electrical conductor and the number of turns w are preferably identical to those of the first and second preferred embodiments. The first, second, and third coils are preferably connected to each other in such a way that they support each other and together are dimensionally stable and freestanding in space.

[0170] The distance between the sub-coils 221, 222 in the X-direction is perpendicular to the coil axis A relative to their dimensions, i.e., in planes parallel to the axis A. Figure 3 The YZ plane shown is dimensioned such that the sub-coils 221, 222 act like a single coil (Helmholtz coil). This condition preferably applies to all in Figure 3 shown partial coils.

[0171] The charger 300 of the third preferred embodiment includes a control unit 350, which is configured to control each coil separately and to generate an alternating current in the respective windings. Each coil or the corresponding sub-coils thus generate an individual alternating magnetic field.

[0172] As in the preceding embodiments, each coil is part of a separate resonant circuit, the elements of which are housed in the control unit 350. Regarding the magnitude of the alternating current generated in each coil and the design of the resonant circuits, reference is made to the descriptions of the preceding embodiments.

[0173] When the control unit 350 generates the alternating current in the coil pairs / sub-coils 311 and 312, the individual alternating magnetic field located within the coil along the coil axis A passes through the sub-coils 311, 312 and over the superposition area located between the sub-coils.

[0174] The partial coils 311 and 312 therefore generate the alternating magnetic field in the same way as the coil 210 in the second preferred embodiment. These explanations apply to all in Figure 3 shown partial coils of the corresponding coils.

[0175] The individual alternating magnetic fields of all coils superimpose in a common area to form the alternating magnetic field that reaches implant I.

[0176] The alternating magnetic field reaching the pacemaker I has sufficiently high and homogeneous values ​​in the common area over large spatial regions around the origin of the coordinate system to trigger the magnetization section (Wiegand wire) of the pacemaker I to generate the charging pulse or to cause the core used for ordinary induction to flow through it to generate the charging pulse.

[0177] The control unit 350 can change the orientation of the resulting alternating magnetic field by controlling the respective coils differently and varying the alternating current flowing in the corresponding windings. If the orientation of the resulting alternating magnetic field is only required in a plane and not in space, one of the three coils is unnecessary.

[0178] When the charger 300 is used as intended, the patient P is preferably moved along the Z-axis through the partial coils 331, 332 until the upper body of the patient P and the pacemaker I are located in the common area. In this embodiment as well, this movement of the patient occurs without contact with any of the coils or their elements.

[0179] In this case, as in the other embodiments, the patient P can be positioned, for example, on a body support or couch.

[0180] All embodiments of the charger according to the invention described above have in common that the alternating magnetic field located within the coil(s) along the corresponding coil axis is used to charge the energy storage device. The alternating magnetic field, or rather its magnetic flux density B, is so strong and largely homogeneous over long distances in these areas of the coil(s) that precise knowledge of the implant's (pacemaker's) position is of secondary importance if the direction of the axis of the magnetization section or the longitudinal extent of the core coincides, to a first approximation, with the axis of the magnetic field vector.

[0181] Furthermore, all embodiments allow the vector of the alternating magnetic field to be pivoted / rotated without changing the amplitude of the magnetic flux density B. This is achieved by mechanically pivoting / rotating the coil(s) and / or by changing the superimposed alternating magnetic fields without contact with the patient. This allows for extremely reliable alignment of the magnetic field vector along the longitudinal axis of the core or the axis of the magnetization section, and thus in the direction of travel of the remagnetization wave.

Claims

1. Charging device (100, 200, 300) for contactless charging of an energy storage device of an implant (I) implanted in a body of a living being, comprising: at least one free-standing coil (110, 210) extending along a coil axis and configured to generate an alternating magnetic field; wherein the body, during intended use of the charging device (100, 200, 300), is spatially arranged relative to the coil (110, 210) in such a manner that the alternating magnetic field, which extends within a region inside the coil along the coil axis, penetrates into the body for charging the energy storage device.

2. Charging device (100, 200, 300) according to claim 1, wherein the charging device is configured to rotate a vector of the alternating magnetic field at least spatially two-dimensionally for charging.

3. Charging device (100, 200, 300) according to claim 1 or 2, wherein the charging device is configured to rotate the vector of the alternating magnetic field for charging without changing the corresponding amplitude.

4. Charging device (100, 200, 300) according to claim 1, 2 or 3, wherein the body, during intended use of the charging device, is arranged relative to the free-standing coil in such a manner that a longitudinal axis of the body extends in the direction of the coil axis and is located within the coil, wherein the alternating magnetic field reaches the location of the implant.

5. Charging device (100, 200, 300) according to claim 2, 3 or 4, further comprising: a suspension configured to hold the free-standing coil and configured to pivot the coil relative to the body about at least one axis, preferably two axes, for rotating the vector, wherein the charging device is configured to control the suspension to pivot the coil into a specific orientation relative to the body for optimizing charging of the energy storage device.

6. Charging device (100, 200, 300) according to claim 5, wherein the suspension which supports the coil is displaceable relative to the body and / or a body support for supporting the body is displaceable relative to the coil, and wherein the charging device is configured to displace the suspension and / or the body support in order to bring the coil, for optimizing the charging of the energy storage, into a certain position relative to the body.

7. Charging device (100, 200, 300) according to claim 5 or 6, wherein the charging device comprises a receiver unit configured to either receive or interrogate a quality signal generated in the implant and reflecting the efficiency of charging, and the charging device is configured, depending on the quality signal, to pivot the coil, for optimizing the charging, into the certain orientation and / or bring it into the certain position.

8. Charging device (100, 200, 300) according to one of the previous claims, wherein a magnetic flux density of the alternating magnetic field along the coil axis comprises a value B, wherein 1.0 mT < = B < = 20.0 mT , preferably 2.0 mT < = B < = 20.0 mT , 2.5 mT < = B < = 8.0 mT , 3.5 mT < = B < = 7.0 mT , 4.5 mT < = B < = 6.0 mT , 4.8 mT < = B < = 5.2 mT , or 5.0 mT = B .

9. Charging device (100, 200, 300) according to one of the claims 1, 2, or 3, wherein the coil is composed of two partial coils spaced apart from one another by a distance R1 along the same axis, which cooperate in such a manner that the alternating magnetic field extends along the coil axis through the partial coils and through a region located between the partial coils; wherein preferably R1 is equal to D / 2 (Helmholtz coil) and the body, during intended use of the charging device, is arranged relative to the partial coils in such a manner that the preferably predominantly homogeneous alternating magnetic field, which is located between the partial coils, penetrates into the body for charging the energy storage device.

10. Charging device (100, 200, 300) according to claim 9, further comprising: a suspension configured to hold the two partial coils of the first coil and configured to pivot the first coil relative to the body about at least one axis, preferably two axes, for rotating the vector, wherein the charging device is configured to control the suspension in order to pivot the two partial coils of the first coil into a specific orientation relative to the body for optimizing charging of the energy storage device.

11. Charging device (100, 200, 300) according to claim 9, wherein the charging device is configured to pivot the two partial coils of the first coil, for optimizing charging of the energy storage device, into a specific orientation relative to the body as a function of a quality signal emitted by the implant and reflecting the efficiency of the charging.

12. Charging device (100, 200, 300) according to claim 8 or 9, further comprising: a second coil extending along a coil axis and composed of two partial coils arranged at a distance R2 from one another in such a manner that a region is formed between the partial coils of the second coil, wherein the coil axes of the first and second coils extend transversely, preferably perpendicularly, to one another, such that the magnetic fields located between the partial coils of the first and second coils overlap in a common region, and the charging device is configured to control the first coil and the second coil, for optimizing charging of the energy storage device, in such a manner that a direction of the vector of the alternating magnetic field in the overlap region rotates two-dimensionally (in a plane).

13. Charging device (100, 200, 300) according to claim 12, further comprising: a third coil extending along a coil axis and composed of two partial coils arranged at a distance R3 from one another in such a manner that a region is formed between the partial coils of the third coil, wherein the coil axes of the first, second, and third coils extend transversely to one another, preferably along spatial coordinates X, Y, and Z, such that the magnetic fields located between the partial coils of the first, second, and third coils overlap in a common region, and the charging device is configured to control the first coil, the second coil, and the third coil, for optimizing charging of the energy storage device, in such a manner that the direction of the vector of the alternating magnetic field in the overlap region rotates three-dimensionally.

14. Charging device (100, 200, 300) according to claim 11 or 12, wherein the charging device is configured to either receive or interrogate a quality signal generated in the implant reflecting the efficiency of charging, and the charging device being configured to bring the vector of the alternating magnetic field in the overlap region into a defined position.