CN112564247A - Implantable device - Google Patents

Implantable device Download PDF

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Publication number
CN112564247A
CN112564247A CN202011345535.4A CN202011345535A CN112564247A CN 112564247 A CN112564247 A CN 112564247A CN 202011345535 A CN202011345535 A CN 202011345535A CN 112564247 A CN112564247 A CN 112564247A
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coil
receiving
transmitting
compensation
implantable device
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CN202011345535.4A
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Inventor
肖春燕
程丁宁
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Beihang University
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Beihang University
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    • H—ELECTRICITY
    • H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
    • H02J—CIRCUIT ARRANGEMENTS OR SYSTEMS FOR SUPPLYING OR DISTRIBUTING ELECTRIC POWER; SYSTEMS FOR STORING ELECTRIC ENERGY
    • H02J7/00—Circuit arrangements for charging or depolarising batteries or for supplying loads from batteries
    • H02J7/02—Circuit arrangements for charging or depolarising batteries or for supplying loads from batteries for charging batteries from ac mains by converters
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01F—MAGNETS; INDUCTANCES; TRANSFORMERS; SELECTION OF MATERIALS FOR THEIR MAGNETIC PROPERTIES
    • H01F27/00—Details of transformers or inductances, in general
    • H01F27/28—Coils; Windings; Conductive connections
    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01F—MAGNETS; INDUCTANCES; TRANSFORMERS; SELECTION OF MATERIALS FOR THEIR MAGNETIC PROPERTIES
    • H01F38/00—Adaptations of transformers or inductances for specific applications or functions
    • H01F38/14—Inductive couplings
    • H—ELECTRICITY
    • H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
    • H02J—CIRCUIT ARRANGEMENTS OR SYSTEMS FOR SUPPLYING OR DISTRIBUTING ELECTRIC POWER; SYSTEMS FOR STORING ELECTRIC ENERGY
    • H02J50/00—Circuit arrangements or systems for wireless supply or distribution of electric power
    • H02J50/005—Mechanical details of housing or structure aiming to accommodate the power transfer means, e.g. mechanical integration of coils, antennas or transducers into emitting or receiving devices
    • H—ELECTRICITY
    • H02—GENERATION; CONVERSION OR DISTRIBUTION OF ELECTRIC POWER
    • H02J—CIRCUIT ARRANGEMENTS OR SYSTEMS FOR SUPPLYING OR DISTRIBUTING ELECTRIC POWER; SYSTEMS FOR STORING ELECTRIC ENERGY
    • H02J50/00—Circuit arrangements or systems for wireless supply or distribution of electric power
    • H02J50/10—Circuit arrangements or systems for wireless supply or distribution of electric power using inductive coupling
    • H02J50/12—Circuit arrangements or systems for wireless supply or distribution of electric power using inductive coupling of the resonant type

Abstract

The application discloses implantable equipment and electric energy transmitting and receiving unit and electric energy transmission device thereof, this electric energy transmitting unit includes first ferrite film and installs the transmitting coil in this first ferrite film, the transmitting coil is for the bipolar coil including a plurality of coils, this electric energy receiving unit includes second ferrite film and installs the receiving coil in this second ferrite film, the receiving coil is for the bipolar coil including a plurality of coils. The transmitting coil and the receiving coil both adopt bipolar coils, and compared with a unipolar coil, the parallel structure of the bipolar coils can improve the wireless power transmission efficiency and further improve the electromagnetic safety of the wireless power transmission device.

Description

Implantable device
The present application is a divisional application of the chinese invention patent application entitled "implantable device and its power transmitting and receiving unit and power transmitting device" with application number 2018104913549.
Technical Field
The present invention relates to an implantable device.
Background
More and more implantable devices, such as cardiac pacemakers, brain pacemakers, etc., are being developed in the current field of medical devices.
Typically, the implantable device is self-contained with a disposable battery. When the battery row is exhausted after a period of use, the implantable device needs to be removed and re-implanted in the body. This procedure is not only traumatic, but also costly and relatively cumbersome. Therefore, how to realize wireless power supply to the implantable device becomes a technical problem to be solved in the field.
Disclosure of Invention
In view of the above, the present application proposes an implantable device.
According to one aspect of the present application, there is provided a power transmitting unit of an implantable device, the power transmitting unit including a first ferrite film and a transmitting coil mounted to the first ferrite film, the transmitting coil being a bipolar coil including a plurality of coils.
Optionally, the electric energy transmitting unit further includes a transmitting end compensation circuit, where the transmitting end compensation circuit includes a first compensation inductor, a first compensation capacitor, and a second compensation capacitor, where the second compensation capacitor is connected in series with the transmitting coil, and the second compensation capacitor and the transmitting coil connected in series are connected in parallel with the first compensation capacitor and then connected in series with the first compensation inductor.
Optionally, the bipolar coil comprises a first coil element and a second coil element which are coplanar and adjacently arranged, wherein the first coil element and the second coil element are semicircular and are oppositely spliced into a circular or elliptical shape.
Optionally, the transmitting coil has a single-layer, double-layer or multi-layer structure; and/or
The transmitting coil is made of litz wires.
Optionally, the transmitting coil is closely attached to the first ferrite film.
The application provides a power receiving unit of an implantable device, which comprises a second ferrite film and a receiving coil arranged on the second ferrite film, wherein the receiving coil is a bipolar coil comprising a plurality of coils.
Optionally, the power receiving unit further includes a receiving end compensation circuit, where the receiving end compensation circuit includes a third compensation capacitor, and the third compensation capacitor is connected in series with the receiving coil.
Optionally, the electric energy receiving unit further includes a rectifying and filtering circuit, the rectifying and filtering circuit includes a bridge rectifier circuit, and a fourth capacitor and a second inductor for filtering, and the fourth capacitor is connected in parallel with the bridge rectifier circuit and then connected in series with the second inductor.
Optionally, the bipolar coil comprises a third coil piece and a fourth coil piece which are coplanar and adjacently arranged, and the third coil piece and the fourth coil piece are both semicircular and oppositely spliced into a circular or elliptical shape.
Optionally, the receiving coil has a single-layer, double-layer or multi-layer structure; and/or
The receiving coil is made into a flexible circuit board or a litz wire coil.
Optionally, the wire cross-section of the receiving coil is between 0.0105 mm and 0.1400 mm.
The application provides an electric energy transmission device of implantable equipment, this electric energy transmission device include the electric energy transmitting unit and the electric energy receiving unit, wherein, receiving coil set up in on the casing of implantable equipment, receiving coil with be provided with between the casing of implantable equipment the second ferrite film, transmitting coil and receiving coil interval set up.
Optionally, the area of the transmitting coil is larger than the area of the receiving coil.
Optionally, the area of the transmitting coil is 1.1 to 1.5 times the area of the receiving coil.
Optionally, in an operating state, the plurality of coil elements in the bipolar coil of the transmitting unit have opposite magnetic field directions; the coil elements in the bipolar coil of the receiving unit have opposite magnetic field directions.
An implantable device comprising said electrical energy transmission apparatus is provided.
Optionally, the implantable device is a cardiac pacemaker, a cardiac defibrillator or a cerebral pacemaker.
The transmitting coil and the receiving coil both adopt bipolar coils, and compared with a unipolar coil, the parallel structure of the bipolar coils can improve the wireless power transmission efficiency and further improve the electromagnetic safety of the wireless power transmission device.
Additional features and advantages of the present application will be described in detail in the detailed description which follows.
Drawings
The accompanying drawings, which are incorporated in and constitute a part of this application, illustrate an embodiment of the invention and, together with the description, serve to explain the invention. In the drawings:
fig. 1 is a circuit model of a wireless power transmission apparatus;
fig. 2 is a wireless power transmission apparatus provided in the present invention;
FIGS. 3a and 3b are schematic diagrams of a bipolar coil arrangement;
fig. 4 is a circuit model of a wireless power transmission apparatus provided in the present invention;
fig. 5 is a simplified vector diagram of a circuit model of the wireless power transmission apparatus of fig. 4.
Detailed Description
In addition, the features of the embodiments and the respective embodiments in the present application may be combined with each other without conflict.
The present application will be described in detail below with reference to the accompanying drawings in conjunction with embodiments.
Fig. 1 shows a circuit model of a wireless power transmission apparatus, which ignores the resistance of a transmitting coil but considers the resistance of a receiving coil, and the receiving end uses only one capacitor for compensation, and the circuit structure within the dashed box can be referred to as an LCC-C topology. In FIG. 1, the inductances of the receiver coil and transmitter coil are L, respectively1And L2Neglecting the resistance of the transmitting coil, the resistance of the receiving coil is R2The compensation capacitance of the transmitting terminal is C1And Cf1The compensation inductance is Lf1. Compensation capacitor C1Connected in series with the transmitter coil and then with the compensation capacitor Cf1Connected in parallel and then coupled to the compensation inductor Lf1Are connected in series. Since the compensation inductance is small in the coupling coefficient with the transmitter coil and the receiver coil, the mutual inductance between them is neglected. The mutual inductance between the transmitter coil and the receiver coil is M. The diodes D1, D2, D3 and D4 form a bridge rectifier and the capacitor C0And an inductance L0Can be used to filter out high frequency components and thus provide a battery UbAnd (6) charging.
As shown in FIG. 1, assume that the voltage at ports 1-1' is
Figure RE-GDA0002913806680000041
(terminal 1 is + and terminal 1 'is-), and the voltage at port 2-2' is
Figure RE-GDA0002913806680000042
(terminal 2 is + and terminal 2' is-), and the currents flowing through the transmitting coil, the receiving coil and the power supply are respectively
Figure RE-GDA0002913806680000043
And
Figure RE-GDA0002913806680000044
the direction of the current flow is shown in figure 1. When the angular frequency is ω, the frequency domain equivalent circuit KVL equation is as follows:
Figure RE-GDA0002913806680000045
wherein
Figure RE-GDA0002913806680000046
Figure RE-GDA0002913806680000051
According to Thevenin's theorem, the input equivalent impedance Z can be calculatedeq2And output equivalent impedance Zeq1。
Figure RE-GDA0002913806680000052
Figure RE-GDA0002913806680000053
If the two-port network in the wireless charging device is in a resonant state, the input impedance and the output impedance must reach minimum values to achieve higher efficiency.
If in resonance, the imaginary part of the impedance on both sides should be zero, i.e. Im (Z)eq1) 0 and Im (Z)eq2)＝0。
Im(Zeq2) When 0, H can be obtained11＝0，H21＝0。
H is to be11＝0，H21Substituting equation (5) for 0 to obtain an impedance expression satisfying the matching condition as
Figure RE-GDA0002913806680000054
If the wireless power transmission apparatus is resonated, a set of solutions is obtained as follows:
Figure RE-GDA0002913806680000055
the magnitude and frequency of the current flowing through the two coils will directly affect the electromagnetic radiation and temperature rise in the human tissue. The higher the current, the faster the charging speed, the higher the temperature rise and the faster the rising speed.
When using the LCC-C topology, the current expressions for the transmit coil and the receive coil are
Figure RE-GDA0002913806680000061
Figure RE-GDA0002913806680000062
It can be seen that the current increases with the increase of the power supply voltage, and when the power supply voltage is a fixed value, the current of the transmitting coil is a fixed value, and the induced voltage of the receiving coil is a fixed value.
For wireless power transmission, the charging coil may be a single-polarity coil including a single coil element, or preferably a multi-polarity coil including a plurality of coil elements, which may be selected according to specific operating conditions.
The present invention provides a wireless power transmission device for an implantable apparatus, as shown in fig. 2, preferably comprising a power supply (connected to the power supply when in operation), a transmitting end compensation circuit, a transmitting coil unit, a receiving end compensation circuit, a rectifying and filtering circuit, and a battery (in a preferred embodiment, the battery can be omitted, and at least one circuit can be selected from the receiving end compensation circuit and the rectifying and filtering circuit), wherein the transmitting coil unit and the receiving coil unit form an electromagnetic coupler.
In order to improve the wireless power transmission efficiency and further improve the electromagnetic safety, the transmitting coil and the receiving coil are of a bipolar structure, the transmitting coil is a bipolar coil comprising a plurality of coil elements, the receiving coil is a bipolar coil comprising a plurality of coil elements, as shown in fig. 3a and 3b, the bipolar coil comprises a first (third) coil element and a second (fourth) coil element which are coplanar and adjacently arranged, and the first (third) coil element and the second (fourth) coil element are both semicircular and are oppositely spliced into a circular or elliptical shape.
Specifically, when the current flowing through the unipolar coil is the same as that flowing through the bipolar coil, since the bipolar coil is formed by connecting two coils in parallel, the current flowing through each coil is only half of the current value in the unipolar coil, which enables to improve the wireless power transmission efficiency, thereby improving the electromagnetic safety.
Meanwhile, in the working state, a plurality of coil pieces in the bipolar coil of the transmitting unit have opposite magnetic field directions; the coil elements in the bipolar coil of the receiving unit have opposite magnetic field directions. Therefore, the cross section of the magnetic path formed by the transmitting unit and the receiving unit is approximately semicircular, which is beneficial to the concentration of the magnetic field on one hand, and can reduce the magnetic leakage degree and improve the electric energy transmission efficiency on the other hand.
In addition, the transmitting coil and/or the receiving coil may also adopt a single-layer, double-layer or multi-layer structure, and the double-layer or multi-layer structure may be used to increase the inductance of the coil. The bipolar structure can improve efficiency and is beneficial to safety. Optionally, to reduce the resistance of the transmit coil, the transmit coil is wound with Litz (Litz) wire. Optionally, the transmitter coil is closely attached to the ferrite film in order to increase the inductance of the transmitter coil. Alternatively, the receiving coil is to be implanted in the human body, and the receiving coil may be fabricated as a flexible circuit board. Since an implantable device such as a pacemaker has a metal housing, and eddy currents on the surface of the housing can greatly reduce the induced voltage received by the receiving coil during wireless charging, a ferrite film is arranged between the receiving coil and the pacemaker housing, the receiving end ferrite film is fixed on the pacemaker housing, and the receiving coil is fixed on the receiving end ferrite film (as shown in fig. 3a and 3 b). Optionally, the receiving coil wire cross section is designed to be 0.0105 mm to 0.1400 mm, preferably 1.2mm x 0.072 mm, to reduce losses and heating. Optionally, the size of the transmitting coil is larger than that of the receiving coil, and preferably, the area of the transmitting coil is 1.1 to 1.5 times that of the receiving coil, so that high transmission efficiency can still be obtained when the transmitting coil and the receiving coil are offset. A ferrite film is disposed proximate the transmitter coil and/or the receiver coil.
Fig. 4 shows a circuit model of a wireless power transmission apparatus, in which a receiving end uses only one capacitor for compensation. In fig. 4, the inductances of the receiver coil and the transmitter coil are L, respectively1And L2The resistance of the transmitting coil is R1The resistance of the receiving coil is R2The compensation capacitance of the transmitting terminal is C1And Cf1The compensation inductance is Lf1The compensation inductance is Lf1Has a resistance of Rf1The receiving end compensation capacitance is C2. Compensation capacitor C1In series with the transmitter coil and then with the compensation capacitor Cf1Parallel, final and compensating inductance Lf1Are connected in series. Since the compensation inductance is small in the coupling coefficient with the transmitter coil and the receiver coil, the mutual inductance between them is neglected. The mutual inductance between the transmitter coil and the receiver coil is M.
Transistor S1、S2、S3And S4Form a DC-AC circuit to convert the input voltage UinConversion to AC voltage, diode D1、D2、D3And D4Form a bridge rectifier and a capacitor C0Connected in parallel and then connected with an inductor L0After series connection and bridge rectification, a capacitor C0And an inductance L0Can be used to filter out high frequency components and thus provide a battery UbAnd (6) charging.
Equivalent input resistance at angular frequency of omega
Figure RE-GDA0002913806680000081
Wherein
Figure RE-GDA0002913806680000082
When resonating, the imaginary part Im (Z)in) Where 0, a is 0 and B is 0 and C is 0, i.e. the resonance matching condition is
ω2Cf1Lf11 and ω2L2C21 and
Figure RE-GDA0002913806680000083
equivalent output impedance
Figure RE-GDA0002913806680000084
Wherein
Figure RE-GDA0002913806680000085
When resonating, the imaginary part Im (Z)out) Where 0, a is 0 and B is 0 and C is 0, i.e. the resonance matching condition is
ω2Cf1Lf11 and ω2L2C21 and
Figure RE-GDA0002913806680000086
fig. 5 is a simplified vector diagram of fig. 4. At resonance, the current can be written as:
Figure RE-GDA0002913806680000091
Figure RE-GDA0002913806680000092
Figure RE-GDA0002913806680000093
wherein the content of the first and second substances,
Figure RE-GDA0002913806680000094
the charging unit is equivalent to a resistance load RLWhen receivingTerminal voltage is constant as
Figure RE-GDA0002913806680000095
Current at the receiving end is
Figure RE-GDA0002913806680000096
And the input terminal voltage is
Figure RE-GDA0002913806680000097
Figure RE-GDA0002913806680000098
The input terminal current is
Figure RE-GDA0002913806680000099
The equivalent input impedance, the equivalent output impedance and the input current at the time of resonance can be calculated by the above formula.
The (wireless) power transmission apparatus and the power transmitting unit and the power receiving unit thereof are described above in detail. Furthermore, the present application also provides an implantable device comprising an electrical energy transmission apparatus as described above. When the portable wireless remote control device is used, the receiving unit and the implantable device are implanted into a human body integrally, the transmitting unit and the receiving unit are arranged outside the human body at intervals, and the transmitting unit transmits electric energy to the receiving unit, so that the portable wireless remote control device can be used for charging and can also be used for directly driving the implantable device to work. The implantable device may be a cardiac pacemaker, a cardiac defibrillator or a cerebral pacemaker. In other embodiments, the solution of the present application is also applicable to other types of implantable devices, such as chips implanted under the skin, etc.
The above description is only for the purpose of illustrating the preferred embodiments of the present application and is not to be construed as limiting the present application, and any modifications, equivalents, improvements, etc. made within the spirit and principle of the present application should be included in the scope of the present application.

Claims (5)

1. An implantable device, characterized in that the implantable device comprises an electrical energy transmission means comprising an electrical energy transmitting unit and an electrical energy receiving unit, wherein,
the electric energy transmitting unit comprises a first ferrite film and a transmitting coil arranged on the first ferrite film, the transmitting coil is a bipolar coil comprising a plurality of coils connected in parallel, each coil comprises a first coil part and a second coil part which are coplanar and adjacently arranged, the first coil part and the second coil part are semicircular and are oppositely spliced into an oval shape, and the outermost first winding tail section of the first coil part is connected with the outermost second winding tail section of the second coil part;
the electric energy receiving unit comprises a second ferrite film and a receiving coil arranged on the second ferrite film, the receiving coil is a bipolar coil comprising a plurality of coils connected in parallel, each coil comprises a third coil piece and a fourth coil piece which are coplanar and adjacently arranged, the third coil pieces and the fourth coil pieces are semicircular and are oppositely spliced into an oval shape, and the tail end of the outermost third winding of the third coil piece is connected with the tail end of the outermost fourth winding of the fourth coil piece;
the receiving coil is arranged on the shell of the implantable device, the second ferrite film is arranged between the receiving coil and the shell of the implantable device, and the transmitting coil and the receiving coil are arranged at intervals;
in the working state, a plurality of coil pieces in the bipolar coil of the transmitting unit have opposite magnetic field directions; the coil elements in the bipolar coil of the receiving unit have opposite magnetic field directions,
the transmitting coil and/or the receiving coil are of a double-layer or multi-layer structure.
2. The implantable device of claim 1,
the receiving coil has a single-layer, double-layer or multi-layer structure; and/or
The receiving coil is made into a flexible circuit board or a litz wire coil.
3. The implantable device according to claim 1, wherein the power transmitting unit further comprises a transmit side compensation circuit comprising a first compensation inductance (L)f1) A first compensation capacitor (C)f1) And a second compensation capacitor (C)1) Wherein the second compensation capacitance (C)1) And the transmitting coil (L)1) Said second compensation capacitors (C) connected in series1) And the transmitting coil (L)f1) And the first compensation capacitor (C)f1) Connected in parallel with the first compensation inductance (L)f1) Are connected in series.
4. An implantable device according to claim 3, wherein the power receiving unit further comprises a receive side compensation circuit comprising a third compensation capacitance (C)2) Said third compensation capacitance (C)2) And the receiving coil (L)2) Are connected in series; the power receiving unit further comprises a rectifying and filtering circuit comprising a bridge rectifying circuit and a fourth capacitor (C) for filtering0) And a second inductance (L)0) Said fourth capacitance (C)0) Is connected in parallel with the bridge rectifier circuit and then is connected with the second inductor (L)0) Are connected in series.
5. The implantable device of claim 1, wherein the implantable device is a cardiac pacemaker, a cardiac defibrillator, or a cerebral pacemaker.
CN202011345535.4A 2018-05-21 2018-05-21 Implantable device Pending CN112564247A (en)

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CN110211780B (en) * 2019-05-31 2021-07-09 中南大学 Capacitive network transformer based on flexible circuit board and measuring method thereof
CN112653252B (en) * 2020-12-07 2023-06-20 南京航空航天大学 Optimization method and system for medium-range kilowatt-level magnetic resonance wireless power supply system

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