Electronic implant

Abstract

An electronic implant for implantation in a body of a living being and for monitoring a bodily function, wherein the implant comprises: • an electrode portion, and • a housing with a volume V G in the range of 0.5 <_ V G <_ 4 cm, which receives the following components of the electronic implant: • (i) electronics connected to the electrode portion, • (ii) an energy store for the long-term supply of electrical energy to the electronics, • (iii) an energy receiving portion, which is electrically connected to the energy store and is designed in such a way that it can receive energy in a contactless manner; wherein • the energy receiving portion has at least one coil for receiving the energy and delivering it to the energy store when an external alternating magnetic field generated by an external charging device passes through it, and • the electronics are designed to provide information for spatially adapting an orientation of the alternating magnetic field to the coil axis.

Description

[0001]Electronic implant The invention relates to an electronic implant for implantation into the body of a living being and for monitoring a bodily function. In particular, the invention relates to an electronic pacemaker that is intended to be implanted in / on the human heart. A pacemaker that can be recharged without contact is known from the document US 2021 / 0212586 A1. The pacemaker has a coil that is glued to a ferrite foil. In this respect, the coil is neither an air-core coil nor a core coil. The ability of the coil to collect a magnetic field generated for charging is limited in such a design. The flat design of the coil also leads to a strong opposing field and thus prematurely limits the drawable current.The pacemaker is designed in such a way that, when anchored to the heart, the coil assumes a specific orientation, namely parallel to the skin surface of the pacemaker wearer. This orientation is necessary so that a charging coil arranged on the skin surface can be aligned with the pacemaker coil. If there is even the slightest deviation between the pacemaker coil and the charging coil, the charging current drops rapidly. In addition, the charging coil on the skin surface must generate a very strong alternating magnetic field so that a field adequate for charging even reaches the coil in the pacemaker. The fact that the pacemaker must be anchored in a specific way places an extreme medical burden on the implanting physician.If the anchoring is so poorly done that the alignment of the coil deviates significantly from the desired alignment, this can result in the implanted pacemaker no longer being able to be charged. Against the above background, the object of the invention is to create an implant that can be implanted anywhere in the body, enables extremely short charging times and is simultaneously compact. At the very least, the object of the invention is to create an alternative implant. This object(s) is(are) achieved by an implant according to patent claim 1. Preferred embodiments are the subject of the dependent claims. The electronic implant for implantation in the body of a living being and for monitoring a bodily function, in particular the pacemaker for monitoring and controlling the bodily function, comprises: an electrode section which is to be fastened or arranged as intended on a body section; and a housing which has a volume V. G G3, 3, and which accommodates the following components of the electronic implant: (i) electronics connected to the electrode section, which are configured to monitor at least the body function via the electrode section; (ii) an energy storage device for the long-term supply of the electronics with electrical energy, which can be recharged with electrical energy after discharge; and (iii) an energy receiving section electrically connected to the energy storage device, which is configured to receive energy contactlessly and to deliver it to the energy storage device for recharging the energy storage device; wherein (i) the energy receiving section comprises at least one coil extending along a coil axis and configured to receive the energy and deliver it to the energy storage device when it is penetrated by an alternating magnetic field generated by an external charger,wherein the coil is an air-core coil or includes a magnetically conductive core made up of one or more parts located within the coil and extending along the coil axis, wherein a) the core extends along the coil axis and does not protrude beyond the ends of the coil, or b) the core extends along the coil axis and protrudes beyond at least one end, preferably both ends, of the coil to form a respective field collector, without increasing the cross-section / longitudinal diameter of the core, or c) the core extends along the coil axis and protrudes beyond at least one end of the coil to form a field collector, wherein the cross-section / longitudinal diameter of the core increases, and (II) the coil, when penetrated by the alternating magnetic field,a charging current rectified by a rectifier of preferably the charging current is supplied; (III) the energy receiving section has a magnetic field capturing surface A0 with A0 -3m perpendicular to the coil axis, which is defined by A, 0 SM / B 0 SMis the magnetic flux that passes through a magnetic longitudinal center lying in the direction of the coil axis or a cross-sectional area at a location within the coil as a maximum, and B0 is the external, average flux density of the alternating magnetic field over the magnetic field capture area A0; and (IV) the electronics are configured to supply information for automatically spatially adapting an orientation of the vector of the external alternating magnetic field to the coil axis. According to the invention, the electronics according to (IV) are configured to supply information for automatically correcting a deviation between a spatial orientation of a vector of an internal alternating magnetic field of a charging coil of a charger and the coil axis of the implant, for example to the charger, whereby the implant can be implanted in any spatial orientation.The electronic implant is preferably constructed such that the location of the maximum magnetic flux, which corresponds to the magnetic longitudinal center, is the longitudinal center of the coil. This applies if the energy receiving section is constructed with mirror symmetry. The implant is, for example, a cardiac pacemaker, a brain pacemaker, an organ pacemaker, or an analysis unit. The latter analysis unit is constructed, for example, in such a way that it continuously or at specific intervals determines parameters such as blood pressure and / or blood values ​​and / or records a cardiogram. If the implant is the aforementioned cardiac pacemaker, it is preferably provided to repair (endogenous) control impulses delivered by the body for the heart, i.e. to fully develop them, or to replace missing endogenous control impulses.The implant is particularly preferably a single-chamber pacemaker or part of a multi-chamber pacemaker network that is located in or implanted on the human heart. The pacemaker network has, for example, two or three implants connected via electrical signals, each of which is implanted in a heart chamber, anchored there, and communicate with each other. Depending on the purpose of the implant, the electrode section contains a certain number of electrodes, with one of the electrodes acting as ground. If the implant takes on the function of one of the aforementioned pacemakers, the electrodes are intended to be connected to the part of the body to be stimulated, for example the heart or brain, or are located on or in this part. In general, the aforementioned electrodes can be, for example, cable electrodes.In particular, in this context, the implant preferably includes a cable of a specific length for each cable electrode, which can be laid as intended to a desired region of the body section within the body. At the end of the cable, a preferably spiral-shaped section is formed for anchoring the cable electrode in the region of the body section. Alternatively, the electrode section can also operate without cable electrode(s). In this case, the aforementioned electrodes are formed on an outer surface of the implant, wherein it is implanted such that the electrodes each rest on or in a region of the body section and / or can be anchored there. This embodiment is particularly advantageous when the implant is the pacemaker or part of the pacemaker network, each of which is to be completely implanted in / on the heart.The pacemaker network therefore then includes several implants according to the invention with corresponding electrode sections that are exposed on the outer surface of the respective units. Alternatively, the electrode section can be constructed from a combination of at least one single cable electrode and at least one single electrode formed on the outer surface. In this case, the implant is preferably arranged on the body section such that the electrode formed on the outer surface comes into contact with the corresponding area of ​​the body section and / or is anchored there. The other electrode, i.e., the cable electrode, is guided to another area of ​​the body section and anchored or fastened there. The electronics of the implant according to the invention are configured to monitor at least one or more body functions. These include, for example, the functions of the aforementioned analysis unit, i.e.the recording of data, for example from a cardiogram, blood pressure values ​​or the recording of blood values. In terms of hardware, the electronics for carrying out corresponding functions comprise, for example, a computing circuit with corresponding memory. If the implant is the aforementioned pacemaker or part of the pacemaker network, each of which is to be implanted in / on the human heart, the electronics are configured to monitor the heartbeat and, based on this, to detect whether the heartbeat needs to be controlled. If this is the case, the electronics generates a stimulation pulse, in particular a voltage pulse, or in extreme cases a voltage surge, and delivers this to the body section via the electrode section. With regard to the structure and functions of the pacemaker network, reference is made to the explanations in patent application EP 3756726 A2.In particular, paragraphs [0011-0028] of EP 3756726 A2 are incorporated by reference. The energy storage device for the long-term supply of the implant according to the invention is preferably an electrochemical accumulator that can be recharged, in particular a lithium-ion accumulator. The energy storage device is preferably dimensioned such that it can supply the entire implant with electrical energy for a running time of 0.5, 0.6, 0.7, 0.8, 0.9, 1.0, 1.1, 1.2, 1.3, 1.4, 1.5, 1.6, 1.7, 1.8, 1.9, 2.0 years (charging intervals) without the need to recharge the energy storage device. For example, the energy storage device has a charging capacity of 200 As to 400 As (ampereseconds, coulombs).The energy storage device can have a plurality of energy storage units that are distributed and arranged separately from one another at various positions in the implant, wherein at least one of the or each of the energy storage units is preferably an electrochemical accumulator unit, in particular a lithium-ion accumulator unit. The energy receiving section preferably includes at least one rectifier and at least one smoothing capacitor, which are located between the coil and the energy storage device. The coil delivers the received energy to the smoothing capacitor via the rectifier. In this context, the charging (alternating) current delivered by the coil is rectified by the rectifier and supplied to the energy storage device by the smoothing capacitor.The energy receiving section is configured to receive energy by induction, for which purpose it includes a coil through which the external alternating magnetic field is passed. Depending on the change in the passing magnetic flux, the coil generates the corresponding charging voltage and, via the rectifier, a corresponding charging current flow, which serves to recharge the energy storage device. In other words, the charging voltage is proportional to the frequency and amplitude of the magnetic flux of the alternating magnetic field. In particular, the core according to a) and / or the field collector according to b) or c) is not an element such as a Wiegand wire / pulse wire, which, when the magnetic field changes by a certain amplitude, exhibits a large Barkhausen jump in the form of a Bloch wall running across the wire and therefore induces pulses of the same magnitude in the coil regardless of the frequency of the alternating magnetic field.In general, the material of the core according to a) acts as a magnetic flux conductor, and the material of the field collector according to b) or c) has irregularly magnetically aligned domains. The housing accommodates the aforementioned components—i.e., the electronics, the energy storage unit, and the energy receiving section—in its interior, preferably hermetically sealing them. The enclosed volume V. G of the housing is preferably a maximum of 1.5 cm 3 , 2 cm 3 , 3 cm 3 or 4 cm 3 where 1 cm 3is preferably excluded. The electrode section is constructed as already explained above. The implant according to the invention is thus an autonomously operating implant that performs its functions independently, without requiring interaction with a control unit located outside the body. The implant is constructed according to the invention such that the energy receiving section has a magnetic field capture area A0 with A0 -3m, which is perpendicular to the coil axis and defined by A0 SM / B0. SMis the magnetic flux which passes through a magnetic longitudinal center lying in the direction of the coil axis, which corresponds to a cross-sectional area of ​​the coil at a specific location within the coil, as a maximum, and B0 is the external, average flux density across the magnetic field capture area A0; and the coil is designed such that, when the alternating magnetic field is present, it preferably supplies the charging current with a strength in a range of approximately 200 mA. Values ​​of approximately 200 mA are preferably excluded from the charging current range. The external alternating electromagnetic field (B0) is preferably generated such that it is aligned in the direction of the coil axis, i.e. the B vector points in the direction of the coil axis. The core according to a) and / or field collector according to b) or c) ensures that the alternating electromagnetic field is conducted into the core with increased intensity via a larger magnetic field capture area (field collecting area) A0.In other words, the field collector ensures that the magnetic flux density within the coil - n*B0 - increases sharply. The magnetic field capture area A0 is located along the coil axis at a certain distance from the end of the core according to a) or the field collector according to b) or c) and runs perpendicular to the coil axis. It is larger than the core according to a) or the field collector according to b) or c). In the case of the air coil, the magnetic field capture area is located in the longitudinal center of the coil. The magnetic field lines that enclose the magnetic field capture area A0 enter the coil (e.g., via the field collector according to b) or c) and / or the core according to a), b) or c)) and pass through the longitudinal center of the coil, which lies in the direction of the coil axis. The magnetic field capture area A0 results from the maximum magnetic. SMin the magnetic longitudinal center or by a cross-sectional area of ​​the coil at a specific location on the coil axis and the external flux density B0 of the external electromagnetic alternating field across A according to the relationship 0 ng A0= In a symmetrical design, especially a mirror-symmetrical design, of the energy receiving section, the magnetic longitudinal center, which corresponds to the location of the cross-sectional area of ​​the coil through which the maximum magnetic flux passes, and the (geometric) longitudinal center of the coil coincide. The following applies to the core and field collector according to b) or c): The length of the core pointing in the direction of the coil axis is denoted by l. K , the length of the field collector pointing in the direction of the coil axis with l FK and the diameter of the field collector perpendicular to the coil axis with D FK, applies constructively in approximation under the assumption of circular cross-sections of the core and field collector running perpendicular to the coil axis A charger preferably generates the external electromagnetic alternating field, preferably with a magnetic flux density of B0 = 0.02 mT, 0.04 mT, 0.1 mT, 0.2 mT, 0.5 mT, 1 mT, 2 mT, 3 mT, 4 mT, 5 mT, 6 mT, 7 mT, 8 mT, 9 mT, 10 mT, 11 mT, 12 mT, 13 mT, 14 mT, 15 mT, 16 mT, 17 mT, 18 mT, 19 mT, or 20 mT, and a frequency f = 0.5 kHz, 1 kHz, 2 kHz, 3 kHz, 4 kHz, 5 kHz, 6 kHz, 7 kHz, 8 kHz, 9 kHz, 10 kHz, 11 kHz, 12 kHz, 13 kHz, 14 kHz, 15 kHz, 16 kHz, 17 kHz, 18 kHz, 19 kHz, 20 kHz, or f > 20 kHz, or from f = 21 kHz in 1 kHz steps up to a maximum of 1.5 MHz. The magnetic flux density B0 is intended to be constant and homogeneous over a large spatial area of ​​the implanted implant, for example, in the heart region of a person where the small implant is located on / in the heart as a pacemaker.The field collector(s) according to b) or c) plus the core result in an amplification n of the magnetic flux density within the coil, where – compared to the case where no field collector is provided – n >= 50, 60, 70, 80, 90, 100, 110, 120, 130, 140, 150, 160, 170, 180, 190, 200. This results in a maximum core flux density B prevailing within the core (amplification 200) for a spatially homogeneous magnetic flux density in the vicinity of the coil of, for example, B0=1mT. Kof 0.2T. Resulting values ​​of the voltage / current are sufficient to supply the energy storage device with sufficient energy for recharging, even if the frequency f of the generated alternating magnetic field is in the low ranges mentioned, for example at 20 kHz. Preferably, the electronic implant is designed such that the energy receiving section includes a rectifier, the coil is configured, when penetrated by the alternating magnetic field, to generate a charging current rectified by the rectifier, which is supplied to the energy storage device for recharging, and the coil is designed such that, in the presence of the alternating magnetic field, it supplies the charging current with a strength in a range of . Preferably, the coil (6) is designed such that, in the presence of the alternating magnetic field with a frequency in a range of .5 SM in one area - 9 -5Vs, the charging current with the strength in a load. The value SM = 1*10 -9 Vs refers to the minimum possible area of ​​A0 at minimum B0 = 0.02mT and the value SM = 5*10 -5 Vs refers to the maximum area A0=2.5*10 -3 m 2at maximum B0 = 20mT. The coil has, for example, W turns, where preferably W = 10, 20, 30, 40, 50, 100, 200, 300, 400, 500, 600, or 700, or 800. W is a maximum of W = 1000, whereby the lower values ​​mentioned are significantly higher. The winding formed by the W turns can be multi-layered or, preferably, single-layered. The metal wire forming the W turns is made, for example, of copper or, preferably, of the lighter metal aluminum and has a wire diameter of, for example, 60 m, 70 m, 80 m, 90 m, 100 m, 150 m, 200 m, up to 700 m and a circular or rectangular cross-section. The length of coil 6 preferably corresponds to that of core 7, so that the ends of the coil preferably correspond to the ends of the core. The corresponding ohmic resistance is determined from the number of turns W, which are incorporated into the inductance L of the coil, and from the length and cross-section of the metal wire forming the coil.When the alternating magnetic field passes through the magnetic field capture area A0 of the energy receiving section, it enters the coil and thus passes through the coil, causing the coil to generate the charging current. Due to the drawn charging current in the specified area, the coil generates a counter-field within the coil through self-induction, which weakens the external field permeating the coil. The difference between the external field and the counter-field results in the useful field driving the charging current. The strength of the counter-field is proportional to the product of the charging current strength and the number of turns, i.e., I. GL *W. In this respect, it is desirable to keep the number of turns low. However, this leads to the opposite effect that the useful field induces a lower voltage in the coil (EMF). The induced voltage, or EMF, corresponds to the frequency-dependent multiplied by the number of turns W (EMF=-Against this background, when minimizing the implant, the number of turns W of the coil for one of the frequencies of the alternating magnetic field specified above is selected such that the voltage induced in the coil by the intended useful field is sufficiently high for charging the energy storage device, but at the same time is as low as possible, e.g. due to the opposing field, and the charging current lies in the specified range between 20mA and 2A. If this cannot be achieved for a specific cut-off frequency because the voltage induced by the useful field is too low for charging the energy storage device, the strength of either the external magnetic field (B field) or the magnetic field capture area A0 can be increased by constructing an air coil or core according to a) and / or a field collector according to b) / c).High field strengths over large ranges of the external alternating magnetic field can be generated, for example, with a charging device as described in EP 4035728 A1. Using a compensation capacitor, the alternating current resistance of the coil in resonance or partial resonance operation can be compensated so that the charging current lies in the specified range between 20 mA and 2 A. The compensation capacitor is very particularly preferably selected in terms of its capacitance so that the resonant circuit comprising the coil and compensation capacitor is not in resonance, but rather the frequency of the external alternating magnetic field lies up to 10% above or below the resonant frequency of the resonant circuit. The energy storage device preferably has a maximum charge content of 200 As to 400 As (Coulomb) to ensure long-term power supply to the implant.Because the energy receiving section is designed to generate the charging current in the range of 20mA to 2A, the implant can charge the energy store within a charging time of one hour. The gain n of the magnetic flux density within the core changes depending on the sum of the field collector(s) and the core in the direction of the coil axis. Preferably, the field collector(s) according to b) and / or c) is / are part of the core, in particular monolithic with the core, formed from the same material. Alternatively, the field collector(s) can be a separate element from the core. The implant is preferably constructed such that the core according to a) or b) or c) is a magnetically conductive solid shaft or a magnetically conductive hollow shaft.For example, the core is the magnetically conductive solid shaft and the energy storage device is located next to the solid shaft in the direction of the coil axis and inside or outside the coil. Alternatively, the coil is wound onto the solid shaft and the energy storage device is located radially around the coil axis. For example, the energy storage device can completely encircle the coil or occupy an angular range of over 180° or 270°. The remaining free space, which extends radially and parallel to the coil axis, can be used for other elements of the implant, such as electronic components. Furthermore, for example, the core is the magnetically conductive hollow shaft onto which the coil is wound, and the magnetically non-conductive energy storage device is located inside the hollow shaft.Alternatively, the magnetically conductive energy storage device is located next to the hollow shaft in the direction of the coil axis and inside or outside the coil. Furthermore, for example, the core is a magnetically conductive housing of the energy storage device, onto which the coil is wound. The energy storage device can have a magnetically non-conductive housing and still serve as a carrier body for the coil, whereby the coil forms the aforementioned air-core coil. Particularly preferably, the core and / or the field collector(s) according to b) and / or c) are made of a material with a high (material-specific) relative magnetic permeability and / or the highest possible (material-specific) saturation flux density. Examples of the material are ferrites, in particular soft magnetic ferrites, or amorphous metals, such as SiFe, which is also available under the brand name ARNON, or mu-metals, such as NiFe alloys.The core and / or the field collector(s) is / are, for example, a solid material or a layered structure made up of a plurality of layers. The core can also, for example, be formed partly from a solid material and partly from a layered structure. The layered structure is preferably formed from a plurality of thin layers, such as thin foils or thin sheets, between which electrically insulating layers are arranged. The electrically insulating layers can bond the thin layers to one another. If the core has the layered structure, the individual layers have a thickness of, for example, 0.015 mm, ... , 0.025 mm, ... , 0.035 mm, ... , 0.050 mm. The electrically insulating layers can have the same thickness or be thinner.In particular, it is preferred that the aforementioned elements (core and / or field collectors) are formed from a solid material if the material is the insulator, and that the aforementioned elements (core and / or field collectors) have a layered structure if the material is poorly but to a certain extent electrically conductive. The implant is preferably constructed such that, in order to recharge the energy storage device, the alternating magnetic field with a flux density B0 is generated in the region of the implanted implant as intended, whereby a corresponding charging voltage is induced in the coil, which leads to a charging (alternating) current emitted by the coil and directly or indirectly supplied to the energy storage device, the core and / or the field collector(s) is / are formed from the material having the high saturation flux density, and a geometry of the core and / or the field collector(s) is / are selected such that a core flux density B.K, which results in the core of the coil from the multiplied flux density (B0) reduced by a counter field generated by the charging (alternating) current, lies in the range, in particular, or of the (material-specific) saturation flux density. The magnetic flux density B0 can have the values ​​already mentioned, in particular in the range from 20 T to 20 mT. This magnetic flux density B0 leads to a relatively strong magnetic flux of the alternating magnetic field within the core because the field collector(s) (and the core) concentrate the field accordingly. According to the invention, the material is preferably selected such that the field prevailing in the core, weakened by the counter field, lies close to the saturation flux density or in the mentioned range. This design ensures optimal utilization of the externally generated alternating magnetic field with regard to the size of the core / field collector(s).The charging current is supplied from the coil to the energy storage device, preferably via charging electronics that include at least the rectifier and at least the smoothing capacitor. The saturation flux density mentioned in various places above refers to the material-specific flux density range in which the corresponding magnetization characteristic (BH characteristic) has a kink or transition region, below which the magnetization characteristic is essentially linear and above which the magnetization characteristic runs with a lower gradient (namely, 0). The saturation flux density preferably refers to the flux density at which—with a further increase in the field strength H of the acting alternating magnetic field—the polarization of the material no longer increases.As already mentioned above, the alignment of the implant when charging the energy storage device should preferably be realized such that the external electromagnetic alternating field or the corresponding field vector (B-vector) points preferably in the direction of the coil axis and permeates the coil. This leads to the best possible induction and charging current pulses. The electronics of the implant preferably also have a communication unit via which it can communicate (send and / or receive) with the outside world (outside the body of the living being), in particular for (i) transmitting information for automatically correcting the deviation between the spatial alignment of the vector of the internal magnetic alternating field of the charging coil of the charger and the coil axis of the implant, and (ii) related signals, such as the start signal.Furthermore, the communication unit can preferably communicate with the outside world to transmit setting data, setting commands, analysis data, and / or information data relating to the charge state of the energy storage device. A data memory, for example, together with the aforementioned computing circuit, is preferably provided for storing the data between communications. According to (IV), the electronics are configured according to the invention to provide information for spatially adapting an alignment of the alternating magnetic field to the coil axis, whereby the implant can be implanted in any spatial orientation. For example, the electronics connected to the electrode section are configured to generate the information for the preferably automatic—preferably parallel—alignment of the coil axis, i.e., the field vector of the charger to the coil axis of the implant.In particular, according to claim 1, the electronics according to (IV) are configured to generate the information for automatically correcting the deviation between the spatial orientation of the vector of the alternating magnetic field generated by the charger and the coil axis of the implant, and to transmit it preferably via the communication unit to the charger, thereby allowing the implant to be implanted at any desired location. The alternating magnetic field is generated, for example, by a charging coil of the charger, within which the patient's body is located during charging.According to the invention, according to (IV), the electronics are configured to (i) send a start signal to start the adjustment of the orientation of the alternating magnetic field to the charger via the communication unit or to receive it from the charger via the communication unit, wherein the charger then changes the orientation of the alternating magnetic field according to a movement function, and (ii) subsequently output time information, indicating when the charging current was suitable for recharging, for example to the charger, as the information for correction via the communication unit. The electronics can preferably generate the information by measuring or processing, wherein the information includes, for example, values ​​about amplitudes and / or gradients of induced voltage and / or charging current strength. The generated information thus forms the basis for the implant to be charged in / at any position, i.e.Location and spatial orientation, can be implanted into the body of the living being. In particular, the electronics are preferably configured to detect the gradient and / or the amplitude of the induced charging voltage and / or the charging current driven by the induced charging voltage, and to generate the time information based thereon. The electronics evaluates in particular whether the charging current was suitable for recharging, in particular maximum, for example based on the gradient and / or the amplitude of the charging current, preferably taking into account a charge state of the accumulator. The communication unit sends the time information to the outside world, whereby a higher-level unit receiving the time information, such as the charging device (preferably according to EP 4035728 A1), can use the time information to deduce any position and orientation of the implant.With knowledge of the position and orientation of the implant, the higher-level unit, such as the charger, can align the B-field vector of the alternating magnetic field accordingly to optimize charging. It should be emphasized here that the initial orientation of the B-field vector can take any direction in space, because subsequent adjustment to the position and orientation of the implant is always possible. This also means that no attention needs to be paid to the resulting position and orientation of the implant when implanting the implant. The same applies to the alternative according to patent claim 6. The movement function according to which the charger changes the orientation of the alternating magnetic field, e.g., the B-field vector, can be arbitrary and does not require any special initial orientation of the field.All that is required is that the movement function is a function dependent on time (f(t)), from which the charger can deduce, after running through the movement function, at what point in time the alternating magnetic field had which orientation. If the charger receives the time information from the implant according to the invention after running through the movement function, it can use the movement function to determine the appropriate orientation from the time information. The charger can carry out the previously mentioned orientation of the alternating field according to the following options: - The charger can use a body holder (e.g.Chair or lounger) on which the body is located, preferably rotate about three orthogonal axes and / or linearly displace it; and / or - The charger can rotate a charging coil that generates the alternating magnetic field, preferably about two or three orthogonal axes and / or linearly displace it; and / or - The charger can align the alternating magnetic field, which is preferably generated by a plurality of charging coils, by changing the operating parameters of the charging coils and superimposing individual alternating magnetic fields of the individual charging coils to form the alternating magnetic field with a specific orientation.Particularly preferably, (V) the electronics are configured to (i) detect completion of the spatial adjustment of the orientation of the alternating magnetic field or to receive a signal from the charger via the communication unit, and to output the time information for correction to the charger, which then assumes the final position for charging. Preferably, the time information indicates at least a point in time or a time range at which / in which the charging current for recharging was maximum. The time information is specified, for example, in a time unit (seconds, hundredths of a second, or milliseconds). In general, in addition to the time information, the implant can also output associated current intensity and / or charge information to the charger or transmit it via the communication unit. The point in time is, in particular, a point in time at which the charging current reached a maximum.The time range, on the other hand, is a period of time in which the charging current passed through a maximum. In particular, the time range is defined by including the time of the maximum charging current and the times before and after that in which the charging current was a maximum of x% lower, where x% = 1%, 2%, 3%, 4%, 5%, 6%, 7%, 8%, 9%, 10%. Particularly preferably, the time information indicates, in the form of times or time ranges, the times at which / in which the charging current was at its maximum, wherein the electronics are configured to (i) qualify the times or time ranges as to whether the respective maximum charging current represents a global or local maximum, and (ii) output at least the time or time range corresponding to the global maximum, for example to the charger, as the information for correction. As already mentioned, the electronics evaluates whether the charging current was suitable or not.was maximum, based on the gradient and / or the amplitude of the charging current, preferably taking into account the charge state of the accumulator. The implant particularly preferably transmits times / time ranges of various maxima, in particular all maxima, to the charger. The charger can then decide which orientation of the alternating magnetic field to set for recharging. The implant according to the invention is preferably designed such that the electronics determine the strength of the charging current at regular or irregular intervals and, based on this, determines the time information and stores it for output. As already mentioned, the implant can additionally store the associated current strength and / or charge information for output.This additional current and / or charge information is particularly advantageous when the implant transmits the time information according to local and global maximums. After receiving the time information, including the current / charge information, the charger can decide whether to align the alternating magnetic field according to the local or global maximum for recharging. Preferably, the electronics do not store the charging current strengths for the entire period from the start signal for adjustment until completion of adjustment, but rather only their maximums for later output with the corresponding time information.Alternatively and according to the invention according to claim 6, according to (IV) the electronics are configured to supply information for automatically correcting a deviation between a spatial orientation of a vector of an internal magnetic alternating field of a charging coil of the charging device and the coil axis of the implant, for example to the charging device, preferably via the communication unit, wherein the electronics have a memory in which at least one threshold value corresponding to a specific strength of the charging current is stored, and the electronics are configured to compare the charging current with the threshold value and, when the charging current reaches the threshold value, to supply at least this information for automatically correcting the spatial orientation of the coil axis of the implant to the charging device in a timely manner, preferably immediately and without delay.A temporal connection means that when the charger receives the information for automatic correction of the spatial orientation, it can derive the orientation of the B-vector of the alternating magnetic field that led to the threshold value being reached from the time of receipt. Particularly preferably, the information for automatic correction of the orientation is sent immediately and without delay, whereby this means that the sending is only delayed by the (hardware-related) processing speed of the electronics. When the charger receives the information, it can derive the spatial orientation of the B-vector from the time of receipt, which is virtually identical to the time at which the threshold value is reached. Particularly preferably, a plurality of threshold values ​​are stored in the memory, each of which has a different specific strength, e.g.of the charging current. If the charging current reaches one of the threshold values, e.g. as part of the rotation of the charger around one of the axes of a coordinate system related to the charger, the electronics output at least this information for recording and determining the current spatial orientation of the coil axis of the charger, preferably immediately and without delay, with a view to the corresponding correction. The output is again carried out in particular via the communication unit. The information for the automatic correction of the orientation is output in the same time, in particular immediately and without delay, preferably n times for reliability reasons, where n is preferably 1, 2 or 3. After this, after rotation around, for example, one coordinate axis, the output for the corresponding threshold value would only be carried out again when, for example, the charger changes to the next coordinate axis for rotation.If the charging current reaches one of the multiple thresholds and has previously exceeded a lower threshold, the charger can preferentially discard the information about the lower threshold. For example, the charger travels two or three mutually orthogonal paths and stores the times and thus the positions at which the highest thresholds were reached. The charger is then able to use these times and positions to determine the position of the implant in the patient's body and optimally align its axis parallel.Preferably, (V) the electronics of the implant are configured to (i) detect the completion of the spatial adjustment of the orientation of the alternating magnetic field or to receive a signal from the charger, and (ii) subsequently, based on the instantaneous charging current, send a field change signal to the charger, which signals the charger to increase or decrease the frequency and / or amplitude of the alternating magnetic field, wherein the electronics subsequently signals to the charger what effects the changes in the frequency and / or amplitude of the alternating magnetic field entail. In this context, the implant preferably, according to both variants according to patent claim 1 or 6 and their preferred embodiments, enters a fine adjustment mode in which it knows that the charger is no longer changing its spatial orientation, but rather the frequency and / or amplitude of the alternating magnetic field.In this fine-tuning mode, the implant, for example, sends charging current information at fixed intervals, so that the charger can interpret the effects of changes in frequency and / or amplitude of the alternating magnetic field to compensate for the body-specific attenuation of the magnetic field and to achieve a fixed amplitude of the charging current. The implant according to the invention, in particular the preferred variants of the energy receiving section, is particularly preferably designed and dimensioned such that, with parallel alignment of the B field vector and coil axis and with a magnetic flux density B0 of 0.02 mT to 1 mT of the external alternating magnetic field, an average magnetic flux of 5*10 results at the stated maximum A0. -8 up to 2.5*10 -6Vs (Weber) is established in the core, whereby the magnetic flux refers to the unloaded case without an opposing field. The ohmic resistance R of the coil is significantly exceeded, it is preferred, as already mentioned, for the electronics to have an additional compensation capacitor, and for the alternating magnetic field to be generated at the frequency resulting from the values ​​of the coil, the compensation capacitor, the ohmic resistance, and the load. In other words, the ohmic resistance R essentially limits the size / strength of the charging current. Ultimately, the design of the implant is optimized with regard to the achieved charging current for a predetermined implant size determined by the volume of the housing, e.g., a cylindrical housing, with a coil with W turns and a winding cross-section A, and an external magnetic field B0.>> R) it applies to a first approximation that the charging current is proportional to the ratio of the magnetic flux through the coil to the inductance of the coil. Therefore, the sum of the dimensions of the field collectors and the length of the core in the direction of the coil axis with the diameter of the field collectors is an important measure of the level of the drawable charging current. These parameters influence both the magnetic flux in the core and the inductance of the coil. In the implant according to the invention, the design relationship is preferably implemented such that the choice of electrical parameters causes the charging current to reach its maximum or be up to 10% lower. In connection with the achieved charging current, it should be emphasized that the ohmic resistance R of the coil can be kept very low by a low number of turns while maintaining a high field strength in the core.The lower ohmic resistance generates lower losses and thus results in significantly lower heat generation. This is a crucial factor due to the intended placement of the implant in the human body, e.g., heart, brain, tissue, vessel, or organ. The following can be derived from the explanations of the implant according to the invention and its preferred features: The described design of the implant, particularly of the energy receiving section, opens up the significant possibility of finding an optimum for the respective application of the implant through the use of many variable parameters, for example, as a cardiac pacemaker, brain pacemaker, organ pacemaker, or analysis unit.This optimum can be found by maximizing the magnetic field resulting in the coil (useful field), minimizing the weight, losses, and especially the number of turns W of the coil, and determining the volume of the implant, as a first approximation, by the dimensions of the magnetic components. Given a desired small size and weight and an autonomous operating time of the implant of, for example, one year and a charging time of, for example, less than 30 minutes, the described design of the implant, particularly of the energy receiving section, provides optimization in terms of volume and weight, as a first approximation, by using the largest possible external magnetic field limited by medical standards (< 1 mT), and as a second approximation, by the losses or heating occurring during charging and the field concentration in the coil or core.The implant according to the invention, particularly in its design as a battery-operated, autonomous cardiac pacemaker, is universally applicable and minimized in terms of volume and weight. As a result, it meets high requirements and overcomes technological limitations. For example, the design of the implant allows it to cope with and fulfill the following high requirements: External alternating magnetic field (B charging capacity: 400 As; charging interval > 1 year, charging time < 1 or 0.5 hour, volume < 2 cm³, here maximum power loss < 60 mW. The general rule is: the larger the external magnetic B field, the shorter the charging time. The human body, in conjunction with the exposure time, is determined by the tolerance (medically). In the borderline case, 400 As briefly (10 3 sec) to a charging current of I Gl = 0.4 A. The considerable counter-field resulting from this relatively large charging current, which is proportional to I Gl* W remains manageable due to the low number of turns of b 50 and the fact that the magnetic field capture area(s) is / are sufficiently large in relation to the small spatial size of the implant, despite or even with a low external alternating magnetic field B0, so that the useful field (difference between the magnetic field concentrated in the core and the opposing field) can drive the charging current. In addition, with the small volume of the implant and the construction of the core according to a) and field collector(s) according to b) / c) with a core diameter of d kiron or aluminum losses) due to the small number of turns and the weight of the implant are low. The fact that in the implant according to the invention the magnetic field concentrated in the core runs sufficiently homogeneously through the core and the number of turns W is low means that the coil can preferably be single-layered, which is conducive to high efficiency and a reduction in weight. The requirements mentioned and / or the effects explained can be achieved even when the external alternating magnetic field is generated at high frequencies. The alternating current resistance, which is already low due to the small number of turns, can be further reduced by the compensation capacitor and the partial resonance or resonance operation to optimize the drawable current. The above statements apply equally to the following embodiment. A preferred embodiment is explained below with reference to the attached figures.Figure 1A shows a preferred embodiment of the implant according to the invention, the representation being merely schematic; Figure 1B shows a schematic sectional view of an energy-receiving section of the implant according to the invention; Figure 1C shows the core according to Figure 1B and a corresponding field profile of the alternating magnetic field generated to charge the implant with the design-defining surface A0; Figures 2A to 2C show further embodiments of the implant according to the invention; Figure 3 shows a schematic sectional view of an alternative energy-receiving section of the implant according to the invention; and Figure 4 shows the implant 100 in any desired position in a human body, wherein only two rotation steps enforce the congruent spatial position with the axis of the coil of the charging device as the starting position for optimal charging of the energy storage device of the implant 100.Figure 1A schematically shows the structure of an implant 100 according to the invention. The implant 100 is preferably completely implanted into a human body, whereby, due to the functions of the electronics 3 explained below, the resulting spatial orientation of the implant 100 can be arbitrary. In other words, the physician can implant the implant without having to take the resulting orientation into account. The implant 100 is, for example, a cardiac pacemaker, a brain pacemaker, an organ pacemaker, or an analysis unit. The latter analysis unit is, for example, constructed such that it determines parameters such as blood pressure and / or blood values ​​continuously or at specific time intervals. The implant is particularly preferably a cardiac pacemaker or cardiac pacemaker network that is located in or on the human heart or is to be implanted in these positions.The implant 100 preferably has a housing 1 that accommodates all elements of the implant 100 and is preferably hermetically encapsulated. The housing 1 is made, for example, from titanium or glass. Alternatively, the housing 1 can be made from a biocompatible plastic. An advantage of the plastic is that the housing 1 can be formed by overmolding / encapsulating the components accommodated therein with the plastic. The implant 100 has an electrode section with electrodes 2, which has a certain number of electrodes 2 depending on the purpose of the implant or the bodily function it is intended to monitor / stimulate. The electrodes 2 are intended to be connected to or lie against the body section, for example the heart or brain, that is to be monitored and / or stimulated.The electrodes 2 can, for example, have spiral sections at their ends that are twisted into the body section and thus anchored. One of the electrodes and / or the housing, if electrically conductive, can serve as a ground electrode. In general, the electronic pacemaker or pacemaker network according to the invention can be a pacemaker according to any NBG code. In general, the electrodes mentioned can, for example, be cable electrodes or electrode surfaces exposed on the outer surface. Also accommodated in the housing 1 are electronics 3, which are configured to monitor and / or stimulate a body function via the electrodes 2, and an energy storage unit with a plurality of, preferably two, energy storage units 4a, 4b, which supply the electronics 3 with electrical energy for a long time, as well as charging electronics 9.Preferably, the charging electronics 9 contain a rectifier 9a and a capacitor 9b, which generate a charging (alternating) current I output by the coil 6. L rectify and as I LG to the energy storage units 4a, 4b by the rectifier 9a converting the charging (alternating) current I output by the coil 6 L rectifies and supplies it to the capacitor 9b, and the capacitor 9b then supplies the current I LGto the energy storage units 4a, 4b. The energy storage units, i.e. the one energy storage unit 4a and the preferred, further energy storage unit 4b, are preferably each rechargeable, electrochemical accumulators, for example lithium-ion accumulators, which supply the entire implant 100 with electrical energy for, for example, 0.5 to 1.5 years before they need to be recharged. The energy storage units 4a, 4b therefore serve to provide long-term power to the implant 100. The energy storage units 4a, 4b can be recharged contactlessly, using induction. For this purpose, the implant 100 has an energy receiving section 5. The energy storage unit 4a is located in a peripheral region (see Figure 1B or Figure 2A) or within a core 7 (see Figure 2B), which will be described below.For this reason, the energy storage unit 4a is schematically shown in Figure 1A within the energy receiving section 5. Figure 1B shows a longitudinal section of the inventive energy receiving section 5 of the implant according to a first variant. This includes a coil 6 with, for example, 1000 turns (W = 1000). Particularly preferably, W is well below 1000 and amounts to W < 50, 40, 30, 20, 10. The coil 6 is wound on and around the aforementioned core 7, which extends along a coil axis SA. In this variant, the core 7 is a solid wave. The coil axis SA also corresponds to a longitudinal axis of the implant 100 or the housing 1. At the respective ends of the coil 6 or the core 7 there is preferably a field collector 18a and preferably a further field collector 18b, which are formed from sections of the solid shaft projecting beyond the coil ends in order to homogenize the field in the coil 6.The field collector 18a and / or the further field collector 18b are preferably dimensioned such that their dimensions transverse to the coil axis SA are identical to those of the core 7. In this respect, the field collector(s) 18a, 18b in this variant merely extend the core 7 beyond its ends located in the direction of the coil axis SA. The end of the core corresponds to the end of the coil 6 in the direction of the coil axis SA. A diameter of the core 7 (and the field collectors 18a, 18b) measured perpendicular to the coil axis SA is 1 mm to 3 mm (millimeters) in Figure 1B. Consequently, the coil 6 wound thereon also has a corresponding inner diameter of 1 mm to 3 mm. In this alternative, a length in the direction of the coil axis SA of the field collector(s) 18a, 18b is preferably at least 1%, 2%, 3%, 4%, 5%, 6%, 7%, 8%, 9%, 10%, 20%, 30%, 40%, 50%, 60%, 70%, 80%, 90%, 100% of the total length of the core 7 located within the coil 6.In Figure 1B, this length is specifically between 83% and 65%, particularly preferably 70%, of the total length of the core 7. The core 6 and both field collectors 18a, 18b preferably have a circular cross-section running perpendicular to the coil axis SA. Alternatively, the cross-section can also be rectangular, in particular square. From a view of Figures 1A and 1B together, it is understandable that one energy storage unit 4a of the energy storage device 4 can be arranged radially to the coil axis SA, at least in sections, around the core 7. Preferably, the energy storage unit 4a completely encompasses the core 7, as shown in Figure 2A. The energy storage device or the energy storage unit 4a according to Figure 2A has one, preferably single, housing that is adapted to the outer contour or outer surface of the coil 6. The core 7 and the coil 6 have a circular cross-section running perpendicular to the coil axis SA. As a result, the inner surface orthe surface of the housing of the energy storage device 4a facing the coil 6 is annular in cross-section (transverse to the coil axis SA). In Figure 2A, the energy storage device 4a is accommodated in a single housing that completely surrounds the core 7. For example, the housing of the energy storage device 4 for this arrangement can be wound or bent around the core 7 or the coil 6. Alternatively, the energy storage device 4a can be constructed from a plurality of energy storage units, each having a housing that corresponds to a circular segment around the core 7. When assembled flush, the energy storage units then completely or partially surround the core 7. In comparison to Figure 1B, Figure 2A shows not only the energy receiving section 5, but the entire implant 100 in longitudinal section and a perspective view. This arrangement of the energy storage device or energy storage units 4a gives the entire implant a very compact structure.The preferred, further energy storage unit 4b can be arranged in the direction of the coil axis SA next to the energy storage unit 4a on the coil 6 or next to the coil 6 on one of the field collectors 18a, 18b according to Figure 1B. A length l. K of the core 7 with the field collectors 18a, 18b according to Figure 1B or 1C can be 15 mm to 40 mm, in particular 15 mm to 25 mm, wherein dimensions of the field collector 18a and the further field collector 18b in the direction of the coil axis are preferably in the range 0 < l Kmm, because at the outer end of the field collectors there is a risk that the useful field becomes negative. The invention is not limited to the dimensions mentioned. These are merely examples. The field collectors 18a, 18b can be separate elements from the core 7 or integral components of the core 7. Figure 1B shows both field collectors 18a, 18b monolithic with the core 7 made of a uniform magnetically conductive material. The material is, for example, a ferrite. The monolithic structure is particularly preferred in the case where the material is an insulator or at least a material with poor electrical conductivity, for example, a ferrite, because no or hardly any eddy currents occur. In general, the core and / or the field collectors 18a, 18b are made of a material with a high relative magnetic permeability. r(particularly preferably in a range of 1000), with the highest possible saturation flux density (for example, 0.4 to 0.7 Tesla for ferrites; or 1 to 1.5 Tesla for the amorphous metals mentioned below, such as SiFe) and the lowest possible electrical conductivity, preferably an insulator. The arrangement of the field collector(s) 18a, 18b is only a preferred but essential reason why the energy storage units 4a, 4b of the implant 100 can be charged by induction even at frequencies from 200 kHz to 1.5 MHz with a small size. When the energy storage units 4a, 4b of the implant 100 need to be charged, a charger (not shown) generates an alternating magnetic field with a magnetic flux density (B-field) B0 of approximately 0.1 mT to 1 mT (milli Tesla), which is present homogeneously in a wide area including the implant 100.The field is particularly preferably aligned in the direction of the coil axis SA (B vector) and permeates the coil 6. The alternating magnetic field is, strictly speaking, an alternating electromagnetic field. However, the electrical component of this field is of secondary importance, which is why, in the context of this application, only the alternating magnetic field is referred to. A pure alternating magnetic field, however, is also encompassed by the invention. The frequency f of the alternating magnetic field lies in the range specified above, for example, at 500 kHz. Because the energy receiving section 5 has the explained core 7 with the field collectors 18a, 18b, the core 7 receives sufficient field from this so that the coil 6 has a sufficiently high charging (alternating) current I. L to charge the energy storage units 4a, 4b, which the charging electronics 9 converts into the rectified charging current I GLrectifies. Figure 1C shows the magnetic properties of core 7 with field collectors 18a and 18b. Figure 1C schematically shows the magnetic field capture areas A0. The magnetic field capture areas A0 result from the dimensions of the field collectors 18a, 18b, and the core 7. The magnetic field capture areas A0 shown are, with respect to the design shown, the corresponding magnetic field capture areas at which the parallel field lines of the external alternating magnetic field begin to change their direction through the energy receiving section. The dimensions of the magnetic field capture areas A0 are obtained using the nomenclature from Figure 1B in approximation for housing sizes 1 cm3G3 and r = 103 (r of the design consisting of core and field collectors, and mirror-symmetrical structure) from and exactly from A 0 SM / B0. This shows that A0 is a fundamental value for the design of the implant or pacemaker. The magnetic field capture surfaces A0 are located along the coil axis SA at a certain distance from the respective field collector 18a, 18b and each run perpendicular to the coil axis SA. They are each significantly larger than the corresponding field collector 18a, 18b. The maximum A0 is <= 2.5 * 10 -3 m 2The external alternating magnetic field (B0) is almost homogeneous due to the design of the charger. The magnetic field lines that define the magnetic field capture surfaces A0 enter via the respective field collector and the core 7 and pass through the longitudinal center LM of the coil 6, which lies in the direction of the coil axis SA. If the magnetic field capture surface A0 is displaced by the design in the direction of the respective field collector, it decreases in size. However, if it is displaced virtually in the opposite direction, it remains constant and, depending on r maximum A0. If the charger reverses the polarity of the alternating magnetic field, the situation is identical, with the difference that the field lines passing through the magnetic field capture area enter the other field collector and core 7 and exit again at the opposite field collector. The magnetic field capture areas A0 are, as mentioned, exactly the maximum SMby the magnetic longitudinal center or a cross-sectional area of ​​the coil at a specific location within the coil 6 and the averaged external flux density B0 of the external electromagnetic alternating field over A0 according to the relationship A0= In the case of the mirror-symmetrical design of the energy receiving section shown, this location is the longitudinal center SM of the coil. In the preceding sections, an alternating magnetic field of < 1 mT and a frequency of 500 kHz was assumed to explain the charging of the energy storage device. The invention is not limited to this. The considerations prior to the description of the figures regarding the charging current I GL , the number of turns W, SMand the frequency of the alternating magnetic field, the ohmic resistance of the coil, and an optional compensation capacitor apply equally to this embodiment. Due to the dimensions of the field collector 18a and the further field collector 18b, there is an increased core flux density B K within the core 7. The core flux density B K exceeds the magnetic flux density B0, for example, up to 200 times (B K =200B0). If the magnetic flux density B0 of the alternating magnetic field generated by the charger, which is present in the area of ​​the implant, is 0.1 mT, the core flux density B K in the unloaded state to approximately 20mT. The core flux density B is reduced K However, the counter field occurring within the coil 6, which is caused by the charging (alternating) current I LThe charging current is 400 mA. These values ​​allow the energy storage units 4a, 4b, which together preferably have a charge content of 400 As, to be charged in approximately 15 to 20 minutes. The dimensions of the core 7 or the field collectors 18a, 18b, the parameters of the coil 6, and the remaining elements are preferably selected such that the weight of the entire implant 100 is low and in the range of 4g (grams), preferably less than 3g. The charging current is supplied from the coil 6 to the energy storage unit or the energy storage units 4a, 4b, preferably via the charging electronics 9 shown. Particularly preferably, an amorphous metal, for example SiFe, can be used as an alternative material to ferrite for the core 7 and / or the field collectors 18a, 18b. Such a metal is available on the market, for example, under the brand name ARNON.The core 7 and / or the field collectors 18a, 18b can preferably have a layered structure with individual layers made of the materials mentioned (e.g. ferrite or SiFe) and are then preferably no longer circular but square. In the variant according to Figure 2A, the electronics 3 and the charging electronics are arranged on a circuit board provided with a passage or a flexible circuit board. The circuit board is pushed onto the solid shaft as shown or bent around the solid shaft and ultimately contacted with the connections 41a of the energy storage device or the energy storage unit 4a. Figure 2B shows a further variant of the implant 100 according to the invention, which differs from that shown in Figure 2A in that the core 7a and field collectors 28a, 28b are designed as a continuous hollow shaft.Figure 2C shows the core 7a and the hollow shaft without a housing, as well as the corresponding magnetic properties of the core 7a with field collectors 28a and 28b. The statements regarding Figure 1C apply analogously to Figure 2C. Furthermore, the energy storage device 4 or the energy storage unit 4a and the circuit board with the electronics 3 and the charging electronics are inserted into the hollow shaft. The electronics 3 are preferably wired 3-dimensionally and cast as a body into the hollow shaft. The hollow shaft 7a is preferably formed from the magnetically conductive material already mentioned with reference to Figures 1A, 1B, and 2A. The coil 6 is wound on an outer surface of the hollow shaft.Particularly preferably, two energy storage units are accommodated within the hollow shaft 7a, between which the electronics 3 are located and which are each located at the outer end within the hollow shaft 7a in order to homogenize and increase the magnetic flux in the coil 6 and to reduce the field density on the surface of the magnetically conductive hollow shaft 7a. Alternatively, the hollow shaft can merely form a carrier body for the coil 6, which is made of a magnetically non-conductive material. In this case, the coil 6 is an air coil. Figure 3 shows a longitudinal section of an alternative energy receiving section 5 of the implant 100 according to the invention, wherein the energy receiving section 5 shown differs from that of Figure 1B only in that field collectors 18a, 18b are provided / formed, which have a larger cross-sectional area than that of the core 7. The diameter D. FKThe diameter of the field collectors 18a, 18b is between 5 mm and 10 mm. The core 7 shown in Figure 3 and preferably the field collectors 18a, 18b can also be designed as a hollow shaft. All other elements of the energy receiving section 5 from Figure 3 are identical to those from Figures 1A and 1B, for which reason reference is made to the explanations therein. The energy receiving section 5 can also be inserted into the housing 1 shown in Figures 2A and 2B with all other components. In particular, the arrangement of the energy storage devices 4 or energy storage units 4a can be identical to Figures 2A and 2B. The electronics 3, 9 can be located on one of the field collectors 8a, 8b, accommodated in a recess formed therein, and / or arranged in the core 7 as shown in Figure 3B. The magnetic field capture area A0 likewise has the aforementioned size A0<=2.5*10 -3 m 2The following statements apply to all variants of the implant shown in Figures 1 to 3. The electronics 3 are preferably configured to supply information for the spatial adaptation / correction of the vector (B vector) of the alternating magnetic field of the charging coil of the charger to the coil axis to the charger, whereby the implant 100 can be implanted in any spatial orientation. For example, the electronics 3 connected to the electrode section 2 are configured to generate the information for the preferably automatic—preferably parallel—alignment of the coil axis of the charger to the coil axis of the implant. The information is, in particular, time information in a time unit, such as seconds.According to the invention, the electronics (3) are configured to (i) send a start signal to initiate the adjustment of the orientation of the alternating magnetic field to the charger via a communication unit (not shown) or to receive it from the charger via the communication unit, wherein the charger then changes the orientation of the alternating magnetic field according to a movement function, and (ii) subsequently output the time information, indicating when the charging current was suitable for recharging, to the charger as the information for aligning the coil axis of the charger via the communication unit. The communication unit sends the time information to the outside world, wherein a higher-level unit receiving the time information, such as the charger (preferably according to EP 4035728 A1), can use the time information to deduce any position and orientation of the implant from the time information.With knowledge of the position and orientation of the implant, the higher-level unit, such as the charging device, can align the B-field vector of the alternating magnetic field accordingly to optimize charging. It is important to note that the initial orientation of the B-field vector can take any direction in space, as subsequent adjustment to the position and orientation of the implant is always possible. This also means that the resulting position and orientation of the implant need not be taken into account when implanting the implant. The movement function according to which the charging device changes the orientation of the alternating magnetic field, e.g., the B-field vector, can be arbitrary and does not require any special initial orientation of the field.All that is required is that the movement function is a function as a function of time (f(t)), from which the charger can deduce, after running through the movement function, at what point in time the alternating magnetic field had which orientation, provided the charger was synchronized in time with the implant. If the charger receives the time information from the implant according to the invention after running through the movement function, it can determine the corresponding orientation from the movement function and the time information. The charger can carry out the previously mentioned orientation of the alternating field according to the following options: - The charger can have a body holder (e.g.Chair or lounger) on which the body is located, preferably rotate about two orthogonal axes and / or displace it linearly; and / or - The charger can rotate a charging coil that generates the alternating magnetic field, preferably about two orthogonal axes and / or displace it linearly; and / or - The charger can align the alternating magnetic field, which is preferably generated by a plurality of charging coils, by changing the operating parameters of the charging coils and superimposing individual alternating magnetic fields of the individual charging coils to form the alternating magnetic field with a specific alignment. Particularly preferably, (V) the electronics are configured to (i) detect completion of the spatial adjustment of the alignment of the alternating magnetic field or to receive a signal from the charger via the communication unit, and (ii) subsequently output the time information.The time information preferably indicates at least one point in time or a time range at which / in which the charging current for recharging was maximum. The point in time is, in particular, a point in time at which the charging current reached a maximum. The time range, on the other hand, is a period of time in which the charging current passed through a maximum. In particular, the time range is defined by including the point in time of the maximum charging current and the points in time before and after that in which the charging current was a maximum of x% below the maximum, where x% = 1%, 2%, 3%, 4%, 5%, 6%, 7%, 8%, 9%, 10%.Particularly preferably, the time information indicates in the form of times or time ranges at which / in which the charging current was at its maximum, wherein the electronics are configured to (i) qualify the times or time ranges as to whether the respective maximum charging current represents a global or local maximum, and (ii) output at least the time or time range corresponding to the global maximum, for example to the charger, as the information for adjusting the alternating magnetic field. Particularly preferably, the implant 100 transmits times / time ranges of various maxima, in particular all maxima, to the charger. The charger can then decide which orientation of the alternating magnetic field to set for recharging.The implant 100 according to the invention is preferably designed such that the electronics 3 determines the strength of the charging current at regular or irregular intervals and, based on this, determines the time information and stores it for output. Preferably, the electronics do not store the strengths of the charging current over the entire period from the start signal for the adjustment until completion of the adjustment, but only their maximums for later output with the corresponding time information. Figure 4 serves to explain the corresponding correction method and shows the implant 100 in any position in the body of a human or patient. The charger is constructed in particular according to EP 4035728 A1, wherein the structure of the charger is included here and the axes of rotation of the charging coil mentioned below refer to the axes of rotation shown in EP 4035728 A1.The spatial alignment is achieved in particular by rotational movements of the charging coil, whereby the congruent spatial position with the axis of the charging device coil is enforced by preferably only two rotation steps as the starting position for optimal charging of the energy storage device / accumulator of the implant 100. These rotational movements / steps are explained below: The patient lies with the implant 100 inside the charging device coil, e.g., in the direction of its coil axis (z-axis). In the first step, the charging device coil is rotated - starting from the zero position shown - about an axis orthogonal to the coil axis (rotation axis 1 / Y-axis) by, for example, + / -70° or, if the charging coil has sufficient spatial dimensions, by a maximum of 180°.The coil axis of the charger passes over a local (in special cases global) maximum at angle alpha, determined by a maximum current amplitude occurring in the implant, with the implant outputting the corresponding time information. In the next step, the axis (rotation axis 1 / Y axis) of the charging coil is rotated back to angle alpha and around the second axis orthogonal to the coil axis (rotation axis 2). A second maximum is passed over at angle gamma, again determined using the maximum current amplitude of the implant coil, with the implant again outputting the corresponding time information. The maximum found at angle gamma always forms the global maximum and is also the optimal alignment of the charger, where the direction of the axis of the implant coil and that of the charger coil coincide.If, in a special case, no current maximum was determined in the first step, then the axis of the implant's coil lies in the direction of the rotation axis 1 / Y-axis (simplest case), which is why the coil axis must be brought in the direction of the rotation axis 1 / Y-axis and the maximum found there represents a global maximum. The charger preferably deduces the fact that no maximum was determined from the fact that it does not receive any time information from the implant within a certain period of time and rotates its axis by 90°. This configuration allows a largely optimal charging current to be achieved for any position of the implant in the body. The statements prior to the description of the figures apply to the embodiment and the explained embodiments and modifications accordingly and vice versa.

Claims

1. Electronic implant (100) for implantation into a body of a living being and for monitoring a body function, in particular a pacemaker for monitoring and controlling the body function, wherein the implant (100) comprises: an electrode section (2) which is intended to be attached or arranged on a body section; and a housing which has a volume V G G 3, 3, and which accommodates the following components of the electronic implant (100): (i) an electronic unit (3) connected to the electrode section, which is configured to monitor at least the body function via the electrode section (2); (ii) an energy store (4) for the long-term supply of the electronic unit (3) with electrical energy, which can be recharged with electrical energy after discharge; and (iii) an energy receiving section (5) electrically connected to the energy store (4), which is configured such that it can receive energy contactlessly and deliver it to the energy store (4) for recharging the energy store (4);wherein (I) the energy receiving section (5) has at least one coil (6) which extends along a coil axis (SA) and is configured to receive the energy and deliver it to the energy store (4) when it is penetrated by an alternating magnetic field generated by an external charger, wherein the coil is an air coil or contains a magnetically conductive core (7) which is located in the coil (6) and runs along the coil axis (SA), wherein a) the core (7) runs along the coil axis (SA) and does not protrude beyond ends of the coil (6), or b) the core (7) runs along the coil axis (SA) and, to form a field collector (18a, 18b), over at least one end of the; Coil (6) protrudes without a cross-sectional area of the core (7) increasing, or c) the core (7) runs along the coil axis (SA) and protrudes beyond at least one end of the coil (6) to form a field collector (18a, 18b), wherein a cross-sectional area of the core (7) increases, and (II) the coil (6), when penetrated by the alternating magnetic field, generates a charging current of preferably a maximum of 2A, rectified by a rectifier, which is fed to the energy storage device (4) for recharging; (III) the energy receiving section (5) has a magnetic field capture area A0 perpendicular to the coil axis (SA), with A0<=2.5*10 -3 m 2 possesses which is determined by A 0 SM / B 0 SMis the magnetic flux which passes through a magnetic longitudinal center within the coil (6) lying in the direction of the coil axis (SA) as a maximum, and B0 is the external, average flux density of the alternating magnetic field over the magnetic field capture surface A0;and (IV) the electronics (3) are configured to supply information for automatically correcting a deviation between a spatial orientation of a vector of an internal alternating magnetic field of a charging coil of a charging device and the coil axis of the implant, for example to the charging device, whereby the implant (100) can be implanted in any spatial orientation, wherein according to (IV) the electronics (3) are configured to (i) send a start signal to start the adjustment of the orientation of the alternating magnetic field to the charging device or to receive it from the charging device, which then changes the orientation of the alternating magnetic field, and (ii) output time information indicating when the charging current was suitable for recharging, for example to the charging device, as the information for the correction.

2. Implant (100) according to claim 1, wherein; the time information indicates at least one point in time or a time range at which the amplitude of the charging current or its gradient for charging was maximum.

3. Implant (100) according to claim 2, wherein the time information indicates points in time or time ranges at / in which the charging current was maximum, and the electronics (3) are configured to (i) qualify the points in time or time ranges as to whether the respective maximum charging current represents a global or local maximum, and (ii) output at least the point in time or time range corresponding to the global or local maximum, for example to the charger, as the information for correction.

4. Implant (100) according to one of the preceding claims, wherein the electronics (3) determines the strength of the charging current at regular or irregular intervals and, based thereon, determines the time information and stores it for output. 5.Implant (100) according to claim 1, 2, 3 or 4, wherein (V) the electronics (3) are configured to (i) detect completion of the spatial adjustment of the orientation of the alternating magnetic field or to receive a signal from the charger, and (ii) subsequently output the time information to the charger.

6. Electronic implant (100) for implantation into a body of a living being and for monitoring a bodily function, in particular a pacemaker for monitoring and controlling bodily function, wherein the implant (100) comprises: an electrode section (2) which is to be fastened or arranged as intended on a body section; and. a housing having a volume V G G 3 , m 3, and which accommodates the following components of the electronic implant (100): (i) an electronic unit (3) connected to the electrode section, which is configured to monitor at least the body function via the electrode section (2); (ii) an energy storage unit (4) for the long-term supply of the electronic unit (3) with electrical energy, which can be recharged with electrical energy after discharge; and (iii) an energy receiving section (5) electrically connected to the energy storage unit (4) and configured to receive energy contactlessly and to deliver it to the energy storage unit (4) for recharging the energy storage unit (4); wherein (i) the energy receiving section (5) has at least one coil (6) extending along a coil axis (SA) and configured to receive the energy and deliver it to the energy storage unit (4) when it is penetrated by an alternating magnetic field generated by an external charging device,wherein the coil is an air coil or includes a magnetically conductive core (7) located in the coil (6) and running along the coil axis (SA), wherein a) the core (7) runs along the coil axis (SA) and does not protrude beyond the ends of the coil (6), or b) the core (7) runs along the coil axis (SA) and protrudes beyond at least one end of the coil (6) to form a field collector (18a, 18b) without a cross-sectional area of the core (7) increasing, or c) the core (7) runs along the coil axis (SA) and protrudes beyond at least one end of the coil (6) to form a field collector (18a, 18b), wherein a cross-sectional area of the core (7) increases, and (II) the coil (6), when penetrated by the alternating magnetic field, has a charging, current of preferably a maximum of 2A is generated, which is fed to the energy storage device (4) for recharging; (III) the energy receiving section (5) has a magnetic field capture area A0 perpendicular to the coil axis (SA) with A0<=2.5*10 -3 m 2 possesses which is determined by A 0 SM / B 0 SMis the magnetic flux which passes through a magnetic longitudinal center within the coil (6) lying in the direction of the coil axis (SA) as a maximum, and B0 is the external, average flux density of the alternating magnetic field over the magnetic field capture area A0; and (IV) the electronics (3) are configured to supply information for automatically correcting a deviation between a spatial orientation of a vector of an internal alternating magnetic field of a charging coil of the charger and the coil axis of the implant, for example to the charger, whereby the implant (100) can be implanted in any spatial orientation, wherein the electronics (3) has a memory in which at least one threshold value, which e.g.corresponds to a specific strength of the charging current, is stored, and the electronics (3) are configured to compare the charging current with the threshold value and, when the charging current reaches the threshold value, to supply at least this information to the charging device immediately and without delay for the automatic correction of the spatial alignment of the coil axis of the implant.

7. Implant (100) according to one of the preceding claims 1 to 6, wherein the core (7) is a magnetically conductive housing of the energy storage device, onto which the coil (6) is wound.

8. Implant (100) according to one of the preceding claims 1 to 6, wherein the core (7) is a magnetically conductive solid shaft or a magnetically conductive hollow shaft.

9. Implant (100) according to claim 8, wherein the core (7) is the magnetically conductive solid shaft, and the magnetically conductive energy storage device is located next to the solid shaft in the direction of the coil axis and inside or outside the coil.

10. Implant (100) according to claim 8, wherein the core (7) is the magnetically conductive solid shaft onto which the coil is wound, and the magnetically non-conductive energy storage device extends radially to the coil axis around the coil.

11. Implant (100) according to claim 8, wherein the core (7) is the magnetically conductive hollow shaft onto which the coil is wound, and the energy storage device(s) is / are located within the hollow shaft, preferably one of the energy storage devices at the end of the hollow shaft.Implant (100) according to claim 8, wherein the core (7) is the magnetically conductive hollow shaft onto which the coil is wound, and the magnetically non-conductive energy storage device is located next to the hollow shaft in the direction of the coil axis and inside or outside the coil.

13. Implant (100) according to one of the preceding claims 1 to 12, wherein the coil 14. Implant (100) according to one of the preceding claims 1 to 13, wherein the implant generates the charging current as intended at a frequency f of the external alternating magnetic field, where f is 50 kHz.

15. Implant (100) according to one of the preceding claims 1 to 14, wherein the energy receiving section is constructed such that the magnetic longitudinal center coincides with the longitudinal center of the coil.

16. Implant (100) according to one of the preceding claims 1 to 14, wherein (V) the electronics (3) are configured to (i) detect completion of the spatial adjustment of the orientation of the alternating magnetic field or to receive a signal from the charger, and (ii) subsequently, based on the instantaneous charging current, send a field change signal to the charger, which signals the charger to increase or decrease the frequency and / or amplitude of the alternating magnetic field, wherein the electronics (3) signal to the charger what effects the changes in the frequency and / or amplitude of the alternating magnetic field entail in order to compensate for the body's own attenuation of the alternating magnetic field.

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