本発明は、高周波を送電する送受電器及びそれを用いる無線充電装置に関するものである。特に、人体や生体などの体内に設置された医療機器等へ無線で電力を供給するための電子機器及び充電装置に関する。The present invention relates to a power transmitter/receiver that transmits high-frequency power and a wireless charging device that uses the same. In particular, it relates to an electronic device and charging device for wirelessly supplying power to medical equipment and other devices placed inside the human body or other living organism.
従来の埋め込み型医療機器での無線充電装置は、磁界結合を利用して送電するものである。Conventional wireless charging devices for implantable medical devices transmit power using magnetic field coupling.
例えば、特許文献１には、充電式電源を有する埋め込み式構成部品及び外部無線充電器を備える埋め込み型医療機器が開示されている。当該外部無線充電器は、充電式電源と、皮膚を介して電力を転送するように構成される誘電コイルと、からなり、該無線充電器の再充電のため補助充電器を検出して電力を受けるように構成されているものである。For example, Patent Document 1 discloses an implantable medical device that includes an implantable component with a rechargeable power source and an external wireless charger. The external wireless charger includes a rechargeable power source and an inductive coil configured to transfer power through the skin, and is configured to detect and receive power from an auxiliary charger to recharge the wireless charger.
上記の埋め込み型医療機器では、高周波磁界を用いて電力を送電するため、生体の導電性や誘電特性の影響を受けることなく、高効率に電力を送受電できる反面、誘電コイルにより漏洩磁界を生じる。漏洩磁界により当該医療機器自体やその回路及び内部配線だけでなく、機器に接続された外部配線にも誘導電流を生じてしまう恐れがある。誘導電流の対策は通常フェライトコアを用いるが、フェライトコアの大きさに制約され、医療機器の小型化は困難になる。The implantable medical devices described above transmit power using a high-frequency magnetic field, which allows for highly efficient power transmission and reception without being affected by the electrical conductivity or dielectric properties of the body. However, the induction coil generates a leakage magnetic field. This leakage magnetic field can generate induced currents not only in the medical device itself, its circuits, and internal wiring, but also in the external wiring connected to the device. Ferrite cores are typically used to prevent induced currents, but the size of the ferrite core is a constraint, making it difficult to miniaturize the medical device.
一方、誘導電流の対策が不十分である場合、医療機器は誤作動を起こす可能性が高まる。さらに、電子レンジなどから漏れ出る磁束が、埋め込み型医療機器の誘導コイルを鎖交するとき、予期せぬ誘導電流が流れ、充電式電源を破壊したり、誘導コイルが発熱することにより体内深部の温度の急激な上昇を引き起したりするなど安全性の課題が顕著となる。特許文献１では、３００ｋＨｚの磁界結合により約３Ｗ送電する場合、体内深部の温度は約４℃上昇するとある。
On the other hand, if countermeasures against induced currents are insufficient, the medical device is more likely to malfunction. Furthermore, when magnetic flux leaking from a microwave oven or the like interlinks with the induction coil of an implantable medical device, unexpected induced currents can flow, destroying the rechargeable power supply or causing the induction coil to heat up, resulting in a sudden rise in temperature deep inside the body, posing significant safety issues. Patent Document 1 states that when transmitting approximately 3 W of power through magnetic field coupling at 300 kHz, the temperature deep inside the body will rise by approximately 4°C.
本発明は、上記誘導コイルを用いる外部無線充電器の課題を鑑みなされたものであり、埋め込み型医療機器のための安全性が高い無線充電装置を提供することが課題である。The present invention was developed in consideration of the issues with external wireless chargers that use induction coils, and aims to provide a highly safe wireless charging device for implantable medical devices.
本発明に係る無線充電装置は、生体内への埋め込み型医療機器へ電力を供給するものであって、
少なくともひとつの送電器と、少なくともひとつの受電器とを備え、
前記送電器は２以上の導体平板から、前記受電器は、２以上の導体平板からなり、
前記送電器の導体平板及び前記受電器の該導体平板は、皮膚に対し相互に平行に対向して配置され、
前記送電器の導体平板はその周囲を絶縁体によって覆われていることを特徴とする。 The wireless charging device according to the present invention supplies power to an implantable medical device in a living body,
At least one power transmitter and at least one power receiver are provided,
The power transmitter is made up of two or more conductor flat plates, and the power receiver is made up of two or more conductor flat plates,
the conductive plate of the power transmitter and the conductive plate of the power receiver are arranged parallel to and facing each other with respect to the skin,
The conductor plate of the power transmitter is characterized in that its periphery is covered with an insulator.
本発明に係る無線充電装置により、電界により電力を送電するため、誘導電流の発生や漏洩磁界の影響を受けることなく充電することができる。The wireless charging device of the present invention transmits power using an electric field, allowing charging to occur without being affected by induced currents or leakage magnetic fields.
また、前記送電器の導体平板を皮膚に貼り付けるだけで、前記受電器の導体平板との間で電界により電力を送電することができる。なお、送電器の導体平板は皮膚への影響や医療機器の使用を考慮して絶縁体で覆っても電力伝送に影響しない。Furthermore, simply by attaching the conductive plate of the power transmitter to the skin, power can be transmitted between the conductive plate of the power receiver and the power transmitter via an electric field. Furthermore, taking into consideration the effects on the skin and the use of medical equipment, the conductive plate of the power transmitter can be covered with an insulator without affecting power transmission.
本発明によれば、生体への埋め込み型医療機器において、誘導コイルの使用による漏洩磁界に起因する機器の故障や体内深部の温度を上昇させることなく、安全に高効率の充電を行うことができる。
According to the present invention, in a medical device implanted in a living body, safe and highly efficient charging can be performed without causing equipment failure or an increase in temperature deep inside the body due to leakage magnetic fields caused by the use of an induction coil.
本発明の実施形態について、以下、図を参照しながら説明する。ただし、説明に使用する図面及び以下の説明は、本開示を十分に理解するために提供されるものであり、これらにより特許請求の範囲に記載の主題を限定することは意図されていない。Embodiments of the present invention will be described below with reference to the drawings. However, the drawings used in the description and the following description are provided to provide a thorough understanding of the present disclosure and are not intended to limit the subject matter described in the claims.
本発明に係る無線充電装置について、図１を用いて説明する。図１は、本発明に係る無線充電装置１が配置される環境の一例を示す模式図である。人体２に埋め込み型医療機器３は埋め込まれる。埋め込み型医療機器３は受電器２００を搭載している。埋め込み型医療機器３は例えば、ペースメーカで、心臓へ一定の鼓動を与えるための電気信号を送るほか、生体情報を取得するための電気配線４を有している。埋め込み型医療機器３は、体外に配置されたシート型送電器５から駆動電力を無線で供給される。The wireless charging device according to the present invention will be described using Figure 1. Figure 1 is a schematic diagram showing an example of an environment in which a wireless charging device 1 according to the present invention is placed. An implantable medical device 3 is implanted in a human body 2. The implantable medical device 3 is equipped with a power receiver 200. The implantable medical device 3 is, for example, a pacemaker, and sends electrical signals to provide a regular beat to the heart, as well as having electrical wiring 4 for acquiring biological information. The implantable medical device 3 is supplied with driving power wirelessly from a sheet-type power transmitter 5 placed outside the body.
シート型送電器５は、例えば、図２に示すように皮膚などに貼り付けて使用するものとなる。この場合、シート型送電器５は、皮膚などに貼り付けるための粘着性を有したフィルム６、送電器１００が搭載された回路部７、金属平板からなる送電電極８、絶縁体９で構成される。
また、この場合、皮膚と皮下脂肪からなる生体組織１０を介して、埋め込み型医療機器３へ電力が送電される。このとき、埋め込み型医療機器３は、絶縁体１１、金属平板からなる受電電極１２、受電器２００が搭載された回路部１３から構成される。
絶縁体９、１１は人体に金属が直接接触することによる金属の腐食を防ぐほか、生体親和性の観点から配置される。例えば、パリレンポリマーによるコーティングが用いられる。 The sheet-type power transmitter 5 is used by being attached to the skin or the like, for example, as shown in Fig. 2. In this case, the sheet-type power transmitter 5 is composed of an adhesive film 6 for attaching to the skin or the like, a circuit part 7 on which the power transmitter 100 is mounted, a power transmitting electrode 8 made of a metal flat plate, and an insulator 9.
In this case, power is transmitted to the implantable medical device 3 via biological tissue 10 consisting of skin and subcutaneous fat. In this case, the implantable medical device 3 is composed of an insulator 11, a power receiving electrode 12 consisting of a metal flat plate, and a circuit section 13 on which a power receiver 200 is mounted.
The insulators 9 and 11 are arranged to prevent corrosion of the metal due to direct contact with the human body and to ensure biocompatibility, and are, for example, coated with parylene polymer.
図３は、無線充電装置５の構成例を示すブロック図である。無線充電装置５は、送電器１００、受電器２００、及び金属平板からなる送電電極８、受電電極１２を備える。受電器２００は、送電器１００に搭載した送電電極８から送電される高周波電力を受電電極１２で受電する。送電電極８及び受電電極１２は少なくとも２枚以上の金属平板を配置した構造を取る。送電電極８と受電電極１２は人体組織１０を介して対応配置される。Figure 3 is a block diagram showing an example configuration of a wireless charging device 5. The wireless charging device 5 includes a power transmitter 100, a power receiver 200, and a power transmitting electrode 8 and a power receiving electrode 12, each made of a flat metal plate. The power receiver 200 receives high-frequency power transmitted from the power transmitting electrode 8 mounted on the power transmitter 100 at the power receiving electrode 12. The power transmitting electrode 8 and the power receiving electrode 12 are structured with at least two or more flat metal plates. The power transmitting electrode 8 and the power receiving electrode 12 are positioned in correspondence with each other via human tissue 10.
このような状態において、例えば、ガブリエルらが測定した実験データによると、前記人体組織１０が皮膚と皮下脂肪からなる場合、１．７４ｋＨｚから３０ｋＨｚの間で３．０以上のＱ値を示すため、送電周波数を１．７４ｋＨｚから３０ｋＨｚの間に設定することで高効率に電力を送電することができる。In such a state, for example, according to experimental data measured by Gabriel et al., when the human tissue 10 consists of skin and subcutaneous fat, it exhibits a Q value of 3.0 or more between 1.74 kHz and 30 kHz, and therefore, by setting the transmission frequency between 1.74 kHz and 30 kHz, power can be transmitted with high efficiency.
送受電器の小型化を考慮する場合は、２００ＭＨｚから４００ＭＨｚ付近まで１．０以上のＱ値を示すため、送電周波数を２００ＭＨｚから４００ＭＨｚの間に設定することで小型かつ高効率に電力を送電することができる。When considering miniaturization of the power transmitter and receiver, the Q value is 1.0 or higher from around 200 MHz to 400 MHz, so by setting the transmission frequency between 200 MHz and 400 MHz, power can be transmitted in a compact and highly efficient manner.
結果、埋め込み型医療機器３は少なくとも金属平板２枚を備え、皮膚の表面に前記送電装置５を貼り付けるだけで電界結合により電力を受電できるため、皮膚等の体外より漏洩磁界を大幅に増加させることなく、簡素な装置により、体外の送電器からの必要な電力の高効率給電が実現できる。As a result, the implantable medical device 3 is equipped with at least two metal plates, and can receive power through electric field coupling simply by attaching the power transmission device 5 to the surface of the skin. This allows for highly efficient power supply from an external power transmitter using a simple device, without significantly increasing the leakage magnetic field from outside the body, such as from the skin.
まず、シート型送電器５について説明する。シート型送電器５は外部バッテリ１０１を駆動電力としてＲＦ電源１０２から高周波電力を出力する。送電電極８は差動入力となるため、送電電極８の入力側には、ＲＦ電源１０２の出力インピーダンスとインピーダンス整合を取りながらシングルエンドから差動信号へ変換するための整合回路１０３とバラン１０４が接続される。外部バッテリ１０１は例えばフィルム型のリチウム電池で構成され、ＲＦ電源１０２、整合回路１０３は例えば、ポリイミド系からなるフレキシブル基板上に構成される。
なお、ＲＦ電源１０１は差動出力回路で設計してもよい。その場合、整合回路１０３は差動入力差動出力で構成することで、バラン１０４を取り除くことができる。 First, we will explain the sheet-type power transmitter 5. The sheet-type power transmitter 5 uses an external battery 101 as driving power and outputs high-frequency power from an RF power source 102. Since the power transmitting electrode 8 has a differential input, a matching circuit 103 and a balun 104 are connected to the input side of the power transmitting electrode 8 to convert a single-ended signal to a differential signal while achieving impedance matching with the output impedance of the RF power source 102. The external battery 101 is, for example, a film-type lithium battery, and the RF power source 102 and matching circuit 103 are, for example, configured on a flexible substrate made of polyimide.
The RF power supply 101 may be designed as a differential output circuit. In this case, the matching circuit 103 is configured as a differential input/differential output, so that the balun 104 can be eliminated.
続いて、埋め込み型医療機器３について説明する。送電電極８から送電された高周波電力は受電電極１２で受電される。受電電極１２は整合回路２０１を介して整流回路２０２に接続され、高周波電力を直流電力に変換する。整流回路２０２の他端はバッテリ２０３に接続されており、直流電力が投入され前記バッテリ２０３を充電する。充電されたバッテリ２０３の電力はＤＣ／ＤＣ２０４を介して、例えば、ペースメーカ２０５へ供給される。
この際、図示していないが受電電力の透過量をモニタリングすることで、透過量が大きくなるように整合回路２０１を自動で調整することが可能である。なお、整流回路２０２とバッテリ２０３の間にバッテリ充電用のＤＣ／ＤＣを追加接続することで、バッテリ２０３の充電速度を速めることができる。 Next, the implantable medical device 3 will be described. High-frequency power transmitted from the power transmitting electrode 8 is received by the power receiving electrode 12. The power receiving electrode 12 is connected to a rectifier circuit 202 via a matching circuit 201, and converts the high-frequency power into DC power. The other end of the rectifier circuit 202 is connected to a battery 203, and DC power is input to charge the battery 203. The power of the charged battery 203 is supplied via a DC/DC converter 204 to, for example, a pacemaker 205.
At this time, although not shown, by monitoring the amount of transmitted power of the received power, it is possible to automatically adjust the matching circuit 201 so that the amount of transmitted power increases. Note that by additionally connecting a DC/DC converter for charging the battery between the rectifier circuit 202 and the battery 203, the charging speed of the battery 203 can be increased.
このようにして体外からペースメーカに搭載されたバッテリで電力を供給することができる。
In this way, power can be supplied from outside the body by a battery installed in the pacemaker.
図２に示す送電電極８を図４に示すように銅の金属平板２枚で構成し、それぞれの金属平板１４と金属平板１５とする。ここでは、シート型送電器５の絶縁体９は、絶縁体平板２枚で表現し、それぞれ絶縁体平板１６、絶縁体平板１７とし、ＦＲ４（比誘電率４．７、誘電正接０．０１）で構成する。The power transmitting electrode 8 shown in Figure 2 is composed of two copper metal plates, as shown in Figure 4, designated as metal plate 14 and metal plate 15. Here, the insulator 9 of the sheet-type power transmitter 5 is represented by two insulator plates, designated as insulator plate 16 and insulator plate 17, and made of FR4 (relative permittivity 4.7, dielectric dissipation factor 0.01).
金属平板からなる送電電極８と、絶縁体平板からなる絶縁体９の厚みはそれぞれ３５μｍ、１００μｍとする。生体組織１０は、ここでは比誘電率１８、誘電正接０．７７の豚の皮膚と皮下脂肪を使用する。その厚みは５ｍｍとする。The thicknesses of the power transmission electrode 8, which is made of a flat metal plate, and the insulator 9, which is made of a flat insulating plate, are 35 μm and 100 μm, respectively. The biological tissue 10 used here is pig skin and subcutaneous fat with a relative permittivity of 18 and a dielectric dissipation factor of 0.77. Its thickness is 5 mm.
埋め込み型医療機器３の絶縁体１１は、送電器側の絶縁体９と同様に、絶縁体平板２枚で表現し、それぞれ絶縁体平板１８、絶縁体平板１９とし、ＦＲ４で構成する。受電電極１２は送電電極８と同様に、銅の金属平板２枚で構成し、それぞれの金属平板２０と金属平板２１とする。The insulator 11 of the implantable medical device 3, like the insulator 9 on the power transmitter side, is represented by two flat insulator plates, designated as insulator plates 18 and 19, and made of FR4. The power receiving electrode 12, like the power transmitting electrode 8, is made by two flat copper metal plates, designated as metal plates 20 and 21.
金属平板からなる受電電極１２と、絶縁体平板からなる絶縁体１１の厚みはそれぞれ３５μｍ、１００μｍとする。The thicknesses of the receiving electrode 12, which is made of a flat metal plate, and the insulator 11, which is made of a flat insulating plate, are 35 μm and 100 μm, respectively.
各金属平板１４、１５、２０、２１の少なくとも一辺に導体配線２２、２３、２４、２５を接続する。導体配線２２、２３は、例えば粘着性を有したフィルム６に設けた穴を通して取り出している。粘着性を有したフィルム６は、ここでは比誘電率５．０、誘電正接０．０８からなるポリウレタンからなるドレッシングテープを用いる。導体配線２２、２３、２４、２５の一端を開放端とし、その開放端には、電力を供給する配線を接続するため、例えばＳＭＡコネクタをはんだで固定する。Conductor wiring 22, 23, 24, and 25 are connected to at least one side of each of the metal flat plates 14, 15, 20, and 21. The conductor wiring 22 and 23 are routed through holes in, for example, an adhesive film 6. In this example, the adhesive film 6 is a polyurethane dressing tape with a relative permittivity of 5.0 and a dielectric dissipation factor of 0.08. One end of the conductor wiring 22, 23, 24, and 25 is left open, and an SMA connector, for example, is soldered to this open end to connect wiring that supplies power.
金属平板１４、１５、２０、２１及び絶縁体平板１６、１７、１８、１９は長辺、短辺とも２ｃｍとする。横並びとなる金属平板１４と金属平板１５、金属平板２０と金属平板２１、絶縁体平板１６と絶縁体平板１７、絶縁体平板１８と絶縁体平板１９の間隔はいずれも２ｃｍとする。導体配線２２、２３、２４、２５は長さ約３ｃｍ、直径０．５ｍｍとする。The metal flat plates 14, 15, 20, 21 and the insulator flat plates 16, 17, 18, 19 each have a long and short side length of 2 cm. The spacing between horizontally arranged metal flat plates 14 and 15, metal flat plates 20 and 21, insulator flat plates 16 and 17, and insulator flat plates 18 and 19 is all 2 cm. The conductor wiring 22, 23, 24, 25 is approximately 3 cm long and has a diameter of 0.5 mm.
豚の皮膚と皮下脂肪からなる生体組織１０の比誘電率とＱ値の測定結果を図５に示す。２００ＭＨｚから４００ＭＨｚ付近までは１．０以上のＱ値を示し、３００ＭＨｚ付近で最大値を示す。Figure 5 shows the measurement results of the relative permittivity and Q value of biological tissue 10 consisting of pig skin and subcutaneous fat. The Q value is 1.0 or higher from 200 MHz to around 400 MHz, and reaches a maximum value around 300 MHz.
本例ではＱ値が高い３００ＭＨｚ付近における電力伝送効率を図６に示す。図６は、導体配線２２、２３、２４、２５のそれぞれ一端に、はんだで固定したＳＭＡコネクタと、ベクトルネットワークアナライザの各端子を接続し、送電電極８に接続された導体配線２２、２３から送電された電力を受電電極１２で受電し、導体配線２４、２５から取り出された場合の、送電電力と受電電力の比から得られる電力伝送効率を周波数軸でグラフ化したものである。In this example, the power transmission efficiency at around 300 MHz, where the Q value is high, is shown in Figure 6. Figure 6 shows a graph of the power transmission efficiency on the frequency axis, obtained from the ratio of transmitted power to received power, when an SMA connector fixed with solder and each terminal of a vector network analyzer are connected to one end of each of the conductor wirings 22, 23, 24, and 25, and power transmitted from the conductor wirings 22 and 23 connected to the power transmitting electrode 8 is received by the power receiving electrode 12 and extracted from the conductor wirings 24 and 25.
図６より生体組織１０は、高周波帯では誘電体として振る舞うことが読み取れる。金属平板１４、１５、２０、２１と生体組織１０でコンデンサが形成され、電界結合によって電力が伝送される。結果、皮膚等の体外より漏洩磁界を大幅に増加させることなく、簡素な装置により、体外の送電器からの必要な電力の高効率給電が実現できる。また、このように薄い厚みで送電器５を実現できるため、皮膚の曲率に応じて密着性良く貼り付けることができ、日常生活に支障をきたすことなく、あるいは睡眠中に、埋め込み型医療機器３を充電できる。From Figure 6, it can be seen that the biological tissue 10 behaves as a dielectric in the high frequency band. A capacitor is formed between the metal plates 14, 15, 20, and 21 and the biological tissue 10, and power is transmitted by electric field coupling. As a result, a simple device can be used to efficiently supply the necessary power from an external power transmitter without significantly increasing the leakage magnetic field from outside the body, such as from the skin. Furthermore, because the power transmitter 5 can be realized with such a thin thickness, it can be attached with good adhesion according to the curvature of the skin, allowing the implantable medical device 3 to be charged without interfering with daily life or during sleep.
本例では実験の容易さから電力の入力線路として導体配線２２、２３、及び電力の出力線路として導体配線２４、２５を設けているが、必ずしもこれに沿うものではなく、例えば、金属平板１４、１５及び金属平板２０、２１上にビアホールを設けて電力の入力線路及び出力線路を設けてもよい。これにより引き回し線路による損失を低減できる。In this example, for ease of experimentation, conductor wiring 22, 23 is provided as the power input line, and conductor wiring 24, 25 is provided as the power output line, but this does not necessarily have to be the case. For example, via holes may be provided on metal plates 14, 15 and metal plates 20, 21 to provide the power input and output lines. This reduces loss due to the wiring lines.
あるいは、図示していないが、送電器１００が搭載された回路部７を誘電体フィルム基板で、受電器２００が搭載された回路部１３を誘電体基板で構成し、金属平板１４、１５及び金属平板２０、２１に対して誘電体フィルム基板や誘電体基板を介して対向配置した金属平板をそれぞれ設けることで電界結合により電力を入力、及び出力させることができる。これによりビアホールを設ける必要がなく、製作が容易になる。Alternatively, although not shown, the circuit section 7 on which the power transmitter 100 is mounted can be constructed using a dielectric film substrate, and the circuit section 13 on which the power receiver 200 is mounted can be constructed using a dielectric substrate. By providing metal flat plates 14, 15 and metal flat plates 20, 21 facing each other via a dielectric film substrate or dielectric substrate, respectively, power can be input and output by electric field coupling. This eliminates the need for via holes and simplifies manufacturing.
また、本例では実験の容易さから粘着性を有したフィルム６にドレッシングテープを用いたが、必ずしもこれに沿うものではなく、例えば、金属平板１４、１５を覆う絶縁体１６、１７に粘着性を有する素材を用いてもよい。これにより、皮膚との接触面積を最小化でき、粘着剤による皮膚への影響を低減できる。In addition, in this example, for ease of experimentation, an adhesive film 6 was used as a dressing tape, but this is not necessarily the case. For example, an adhesive material could be used for the insulators 16, 17 that cover the metal plates 14, 15. This minimizes the contact area with the skin and reduces the impact of the adhesive on the skin.
なお、本例では実験の容易さから方形状の金属平板１４、１５、２０、２１および絶縁体平板１６、１７、１８、１９を用いたが、必ずしもこれに沿うものではない。
隣り合う金属平板間の電界結合を低減する形状、例えば、円形状やホームベース状の金属平板を用いてもよい。これにより、隣り合う金属平板間の電界結合を低減でき、電力伝送効率の効率化を実現できる。さらに、絶縁体平板も金属平板電極全体を覆う平板構造や薄膜構造を用いてもよい。これにより、金属平板と皮膚の直接的な接触を防ぐことができ、金属の腐食等を防ぐことができる。 In this example, rectangular metal plates 14, 15, 20, 21 and insulating plates 16, 17, 18, 19 are used for ease of experimentation, but this does not necessarily apply.
Metal plates with a shape that reduces electric field coupling between adjacent metal plates, such as a circular or home plate-shaped plate, may be used. This reduces electric field coupling between adjacent metal plates, improving power transmission efficiency. Furthermore, the insulator plate may have a flat plate structure or a thin film structure that covers the entire metal plate electrode. This prevents direct contact between the metal plate and the skin, preventing metal corrosion, etc.
また、本例では実験の容易さから送電電極８と受電電極１２に同じ面積の方形状の金属平板１４、１５、２０、２１を用いたが、必ずしもこれに沿うものではない。
送電電極と受電電極の位置ずれが生じても保証できるように送電電極の面積を受電電極の面積よりも大きくする、例えば、1.1倍の面積にすることで、２ｃｍ角の受電電極に対し、送電電極は２．２ｃｍ角のサイズとなるため、長辺方向と短辺方向にそれぞれ０．２ｃｍずれても送電電極と受電電極の対向面積は２ｃｍ×２ｃｍを維持することができ、効率の低下を防ぐことができる。
In this example, for ease of experimentation, rectangular metal flat plates 14, 15, 20, 21 having the same area are used for the power transmitting electrode 8 and the power receiving electrode 12, but this is not necessarily the case.
To ensure that there is no misalignment between the transmitting and receiving electrodes, the area of the transmitting electrode is made larger than that of the receiving electrode. For example, by making the area 1.1 times larger, the transmitting electrode will be 2.2 cm square compared to the 2 cm square receiving electrode. Therefore, even if there is a misalignment of 0.2 cm in either the long or short direction, the opposing area between the transmitting and receiving electrodes can be maintained at 2 cm x 2 cm, preventing a decrease in efficiency.
１ 無線充電装置
２ 人体
３ 埋め込み型医療機器
４ 電気配線
５ シート型送電器
６ 粘着性を有したフィルム
７ 送電器１００が搭載された回路部
８ 送電電極
９、１１ 絶縁体
１０ 生体組織
１２ 受電電極
１３ 受電器２００が搭載された回路部
１４、１５、２０、２１ 金属平板
１６、１７、１８、１９ 絶縁体平板
２２、２３、２４、２５ 導体配線
１００ 送電器
１０１ 外部バッテリ
１０２ ＲＦ電源
１０３、２０３ 整合回路
１０４ バラン
２００ 受電器
２０１ 整合回路
２０２ 整流回路
２０３ バッテリ
２０４ ＤＣ／ＤＣ
２０５ ペースメーカ
1 Wireless charging device 2 Human body 3 Implantable medical device 4 Electrical wiring 5 Sheet-type power transmitter 6 Adhesive film 7 Circuit unit on which power transmitter 100 is mounted 8 Power transmitting electrodes 9, 11 Insulator 10 Biological tissue 12 Power receiving electrode 13 Circuit unit on which power receiver 200 is mounted 14, 15, 20, 21 Metal flat plates 16, 17, 18, 19 Insulator flat plates 22, 23, 24, 25 Conductor wiring 100 Power transmitter 101 External battery 102 RF power source 103, 203 Matching circuit 104 Balun 200 Power receiver 201 Matching circuit 202 Rectifier circuit 203 Battery 204 DC/DC
205 Pacemaker
| Application Number | Priority Date | Filing Date | Title |
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| JP2021100362AJP7742628B2 (en) | 2021-06-16 | 2021-06-16 | wireless charging device |
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| JP2021100362AJP7742628B2 (en) | 2021-06-16 | 2021-06-16 | wireless charging device |
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2012253398A (en) | 2009-09-29 | 2012-12-20 | Univ Of Electro-Communications | Device, system, and method for transmitting power and information |
| WO2016135951A1 (en) | 2015-02-27 | 2016-09-01 | オリンパス株式会社 | Medical power supply system |
| JP2020182679A (en) | 2019-05-08 | 2020-11-12 | 古河電気工業株式会社 | Medical devices, extracorporeal units, power transmission sheets, medical devices and location detection methods |
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2012253398A (en) | 2009-09-29 | 2012-12-20 | Univ Of Electro-Communications | Device, system, and method for transmitting power and information |
| WO2016135951A1 (en) | 2015-02-27 | 2016-09-01 | オリンパス株式会社 | Medical power supply system |
| JP2020182679A (en) | 2019-05-08 | 2020-11-12 | 古河電気工業株式会社 | Medical devices, extracorporeal units, power transmission sheets, medical devices and location detection methods |
| Publication number | Publication date |
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| JP2022191877A (en) | 2022-12-28 |
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