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WO2024079570A1 - Liaison à induction multifréquence modulaire pour alimenter sans fil de multiples implants miniaturisés - Google Patents

Liaison à induction multifréquence modulaire pour alimenter sans fil de multiples implants miniaturisés Download PDF

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Publication number
WO2024079570A1
WO2024079570A1 PCT/IB2023/059962 IB2023059962W WO2024079570A1 WO 2024079570 A1 WO2024079570 A1 WO 2024079570A1 IB 2023059962 W IB2023059962 W IB 2023059962W WO 2024079570 A1 WO2024079570 A1 WO 2024079570A1
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WO
WIPO (PCT)
Prior art keywords
coil
frequency
power
resonating
receiving coil
Prior art date
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Ceased
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PCT/IB2023/059962
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English (en)
Inventor
Gian Luca BARBRUNI
Diego Ghezzi
Sandro Carrara
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Ecole Polytechnique Federale de Lausanne EPFL
Original Assignee
Ecole Polytechnique Federale de Lausanne EPFL
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Publication of WO2024079570A1 publication Critical patent/WO2024079570A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/372—Arrangements in connection with the implantation of stimulators
    • A61N1/378—Electrical supply
    • A61N1/3787—Electrical supply from an external energy source
    • 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
    • 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
    • H02J50/40—Circuit arrangements or systems for wireless supply or distribution of electric power using two or more transmitting or receiving devices
    • H02J50/402—Circuit arrangements or systems for wireless supply or distribution of electric power using two or more transmitting or receiving devices the two or more transmitting or the two or more receiving devices being integrated in the same unit, e.g. power mats with several coils or antennas with several sub-antennas
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/372—Arrangements in connection with the implantation of stimulators
    • A61N1/37211—Means for communicating with stimulators
    • A61N1/37217—Means for communicating with stimulators characterised by the communication link, e.g. acoustic or tactile
    • A61N1/37223—Circuits for electromagnetic coupling
    • A61N1/37229—Shape or location of the implanted or external antenna
    • 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
    • H02J2310/00—The network for supplying or distributing electric power characterised by its spatial reach or by the load
    • H02J2310/10—The network having a local or delimited stationary reach
    • H02J2310/20—The network being internal to a load
    • H02J2310/23—The load being a medical device, a medical implant, or a life supporting device

Definitions

  • FIG. 1 further illustrates a standard architecture 100 for a wirelessly powered neural implant 101, which is based on an external transmitter coil 102 (Tx), i.e., external to the patient 105, and an implanted receiver coil 103 (Rx).
  • Tx external transmitter coil 102
  • Rx implanted receiver coil 103
  • the principle in the inductive link between the external transmitter coil 102 (Tx) and the implanted receiver coil 103 (Rx) is that of inducing a magnetic field 104 at a single resonating carrier frequency f0 which is the same for the two coils 102 and 103. If the implanted receiver coil 103 is particularly small, i.e., in the mm-range or sub-mm-range, the efficiency of the standard architecture 100 is extremely low, i.e., 0,01% or below (see G. L. Barbruni, P. M. Ros, D. Demarchi, S. Carrara and D.
  • the maximum averaged Specific Adsorption Rate (SAR) for the human head is set by the Federal Communications Commission (FCC) to 1,6 W/Kg for 1 g of tissue mass measured during 30 minutes of exposure (see IEEE Standards Coordinating Committee. “IEEE standard for safety levels with respect to human exposure to radio frequency electromagnetic fields, 3kHz to 300GHz.” In: IEEE C95. (1992), pp.1–1991).
  • FCC Federal Communications Commission
  • the invention provides a modular multiple frequency coils inductive link system to wirelessly provide power for at least a medical implant at an output of a receiving coil, whereby the receiving coil is configured to be implanted in an organism.
  • the modular multiple frequency coils inductive link comprises a transmitter coil configured to input power from a power supply and induce a first magnetic field at a resonating carrier frequency.
  • the modular multiple frequency coils inductive link further comprises a shifting resonator comprising at least an active integrated circuit, a first coil configured to receive the first induced magnetic field from the transmitter coil by induction at the resonating carrier frequency and convert it to an electrical current, and a second coil configured to transmit the electrical current to the receiving coil by inducing a second magnetic field at a determined frequency different from the resonating carrier frequency, the active integrated circuit connected with both the first coil and the second coil and being configured to receive the power induced at the resonating carrier frequency though the first coil and to use it to drive remaining power reduced due to a power dissipation of the active integrated circuit at P3735PC00 / 0013-571 dpt the determined frequency though the second coil.
  • the receiving coil is configured to receive the power induced by the second coil at the determined frequency and make it available at the output of the receiving coil.
  • the active integrated circuit is further configured to obtain a frequency change from the resonating carrier frequency to the determined frequency by means of a frequency multiplier in case that the determined frequency is greater or equal to the resonating carrier frequency or by a frequency divider in case that the determined frequency is smaller than the resonating carrier frequency.
  • the system further comprises at least a further shifting resonator configured to be operated in a parallel fashion relative to the shifting operator, and at least a further receiving coil configured to receive power induced by the at least one further shifting resonator and make it available at an output of the at least one further receiving coil.
  • the shifting operator and the at least one further shifting resonator are configured to each produce a frequency change from the resonator carrier frequency to a respective determined frequency, and each send power respectively to the receiving coil and to the at least one further receiving coil by inducing at the respective determined frequency.
  • the system further comprises at least a further shifting resonator configured to be operated in a serial fashion relative to the shifting operator, and at least a further receiving coil configured to receive power induced by the at least one further shifting resonator and make it available at an output of the at least one further receiving coil.
  • the at least one further receiving coil is configured to produce a frequency change in the power received from the shifting resonator at the determined frequency to a further determined frequency, and send power to the further receiving coil by inducing at the further determined frequency.
  • the system is configured to wirelessly provide power for a plurality of medical implants respectively each of which is at an output of a corresponding receiving coil from a plurality of receiving coils.
  • the shifting resonator comprises an array of focusing passive resonators corresponding to the plurality of receiving P3735PC00 / 0013-571 dpt coils, and is configured such that active integrated circuit re-transmits the power received at the first coil and transformed by the Integrated Circuit to the plurality of receiver coils using the array of focusing passive resonators.
  • the invention provides a method for wirelessly powering through induction at least one medical implant configured to be implanted in an organism by receiving power through an implant receiving coil.
  • the method comprises inducing with a transmitter coil that inputs power from a power supply, a first magnetic field at a resonating carrier frequency; in a shifting resonator configured to be implanted and comprising an active integrated circuit, a first coil and a second coil: receiving at the first coil the first magnetic field by induction, at the resonating carrier frequency f0 and converting it to an electrical current; operating with the active integrated circuit a frequency change by acting on the electrical current, between the resonating carrier frequency and a determined frequency; inducing a second magnetic field in the second coil corresponding to the electrical current at the determined frequency.
  • the method further comprises receiving at the implant receiving coil the second magnetic field and converting it into power for the at least one medical implant.
  • the method further comprises obtaining with the active integrated circuit a frequency change from the resonating carrier frequency to the determined frequency by means of a frequency multiplier in case that the determined frequency is greater or equal to the resonating carrier frequency or by a frequency divider in case that the determined frequency is smaller than the resonating carrier frequency.
  • figure 1 contains an illustration of a standard architecture for a wirelessly powered neural implant according to prior art
  • figure 2 contains an illustration of a system to wirelessly power a body implant according to an example embodiment of the invention
  • figure 3 contains an illustration of a system to wirelessly power a plurality of body implants according to an example embodiment of the invention
  • figure 4 contains an illustration of a system to wirelessly power body implants with multiple shifting resonators in parallel according to an example embodiment of the invention
  • figure 5 contains an illustration of a system to wirelessly power body implants with multiple shifting resonators in serial fashion according to an example embodiment of the invention
  • figure 6 contains a flowchart illustrating a method according to an example embodiment of the invention
  • figure 7 contains an illustration of a system to wirelessly power a plurality of body implants according to an example embodiment of the invention.
  • a system 200 is configured to wirelessly power at least one body implant (not illustrated in the figure) connected to an implanted receiver coil 201 (Rx) by making use of an external transmitter coil 202 (Tx).
  • the system 200 comprises a replacement of the passive receiver coil 103 of prior art as illustrated in figure 1, with an active structure 203 which splits the power transmission in two blocks.
  • the active structure 203 is also configured to be implanted in a living body (not shown in figure 2).
  • the active structure 203 proposed here may be called «Shifting resonator» (also referred to in figure 2 with reference 203) and comprises an active Integrated Circuit 204 (IC) and a first coil SR0 and a second coil SR1.
  • the first coil SR0 is configured to receive power from the external transmitter coil 202 (Tx) at the resonating carrier frequency f0 and the second coil SR1 to transmit the power received at the first coils SR0 and transformed by the Integrated P3735PC00 / 0013-571 dpt Circuit 204, to the implanted receiver coil 201 at a determined frequency, e.g., f1.
  • the active Integrated Circuit 204 is configured to produce a frequency change between the first coil SR0 and the second coil SR1 of the shifting resonator 203.
  • the two frequencies f0 and f1 can be separately optimized based on the different medium, e.g., air, tissue, bone, as well as for distance, and for power budget.
  • a system 300 very similar to the system 200 may be configured to transmit power from the shifting resonator 203 in parallel to a plurality of implanted receiver coils 2010, 2011, ..., 201n at the frequency f1.
  • the frequency f0 may be 13,56 MHz.
  • a system 400 may be modular: the single external transmitter coil 202 (Tx) sends power to a plurality of shifting resonators 401 1 –401 m at the same frequency f0.
  • the shifting resonators 401 1 –401 m are operated in a parallel fashion.
  • Each shifting resonator 401 1 –401 m produces a frequency change from f0 to a respective determined frequency f1, f2, ..., fm and sends power to at least one corresponding implanted receiving coil 4021–402m at the respective different determined frequency f1, f2, ..., fm, as appropriate, thus limiting the electromagnetic interference.
  • a system 500 exhibits additional features of being powerful and scalable: a new subset of neural implants (not illustrated in figure 5) connected to at least a corresponding receiving coil 501 can be powered only by adding an additional shifting resonator 502 which operates at a new additional frequency f2 obtained from converting the power received from the shifting resonator 203 at the determined frequency f1 to power transmitted in a magnetic field at a further determined frequency f2 different from the determined frequency f1.
  • the corresponding additional shifting resonator 502 is said to be operated in a serial fashion.
  • a system 700 bearing some similarities with the system 300 of figure 3, may be configured to transmit power from a shifting resonator 701 in parallel to a plurality of implanted receiver coils 201 0 , 201 1 , ..., 201 n at the frequency f1.
  • An active Integrated Circuit 702 switches the resonating carrier frequency f0 to the frequency f1 and re-transmits the power received at the first coil SR0 and transformed by the Integrated Circuit 702 to the plurality of receiver coils 201 0 , 201 1 , ..., 201 n using another array of focusing passive resonators 7030, 7031, ..., 703n that are part of the shifting resonator 701.
  • each of the shifting resonators may be configured to work as a data collector in the case of simultaneous data and power transmission, thus allowing for higher bandwidth in the case of data transmission.
  • each shifting resonator 401 1 –401 m transmits/collects data from the implants 402 1 –402 m at the respective different determined frequency f1, f2, ..., fm.
  • PLL phase locked loop
  • the first coil SR0 and the second coil SR1 are fabricated in copper and wired to the active integrated circuit on a PDMS (Polydimethylsiloxane) substrate.
  • PDMS Polydimethylsiloxane
  • the entire shifting resonator 203 (the first coil SR0, the second coil SR1 and the active integrated circuit 204) is then fully encapsulated by PDMS (Polydimethylsiloxane) and can be implanted above the dura.
  • PDMS Polydimethylsiloxane
  • the determined frequency f1 433,92 MHz results to be the optimal operating frequency for power transmission due to the ultra-small size of the receiver (see Ahmadi, Nur, et al. "Towards a distributed, chronically-implantable neural interface.” 20199th International IEEE/EMBS Conference on Neural Engineering (NER). IEEE, 2019).
  • the PTE of this second link is proportional to the coupling coefficient (k 12 2 ) between the second coil SR1 and the receiver coil 201 (Rx), as equation (1) below shows (see D. Ahn and M. Ghovanloo, "Optimal design of wireless power transmission links for millimetre-sized biomedical implants", IEEE Trans. Biomed. Circuits Syst., vol.10, no.1, pp.125-137, Feb.2016).
  • Equation 3 where E rms is the round value of the electric field; ⁇ and ⁇ are respectively the tissue conductivity and density. Following the Maxwell's equation, it is possible to extract the electric field E from the magnetic field B as in equation 4. Equation 4: where fop is the operating frequency and ITx is the flowing current. 2 Therefore, it is worth assuming that the SAR is proportional to ⁇ ⁇ ⁇ ⁇ ⁇ ⁇ ⁇ ⁇ ⁇ .
  • the first inductive link (between the transmission coil 202 P3735PC00 / 0013-571 dpt (Tx) and the first coil SR0) has a PTE of 30%; ii) the power conversion efficiency of the active integrated circuit 204 is 80%; and iii) the power loss due to operation of the frequency multiplier (i.e., PLL based structure as in Barbruni, Gian Luca, et al. "A 20 Mbps, 433 MHz RF ASK Transmitter to Inductively Power a Distributed Network of Miniaturised Neural Implants.” 2021 IEEE International Symposium on Medical Measurements and Applications (MeMeA).
  • the frequency multiplier i.e., PLL based structure as in Barbruni, Gian Luca, et al.
  • the shifting resonator 701 is composed by: i) a receiver SR0, modelled with inductance LSR0 and series resistance RSR0 resonating at the low operating frequency f0 and coupled with the external transmitter coil 202 (Tx) with the coupling coefficient kT x ⁇ SR0; ii) a transmitter SR1, modelled with inductance L SR1 and series resistance R SR1 resonating at the high operating frequency f1; iii) an array of N passive resonators 7030, 7031, ..., 703n (Res), each modelled with inductance L Res and series resistance R Res resonating at f 1 via C Res and iv) the active Integrated Circuit 702 responsible of SR 0 and SR 1 matching at f 0 and f 1 respectively and of the frequency switching from f 0 to
  • Tx and SR 0 work as a standard 2-coils IPT link operating at the low frequency f0 (i.e., 13.56 MHz).
  • SR0 is a single turn circular copper coil with outer diameter of 13.5 mm, trace width of 500 ⁇ m and thickness of 18 ⁇ m coupled with the external Tx.
  • SRF Self Resonance Frequency
  • SR1 is a single turn circular copper coil with outer diameter of 14.7 mm, trace width of 60 ⁇ m and thickness of 18 ⁇ m, designed co-planar with SR0.
  • the array of 37 focusing Res allow an uniform power delivery into the entire area of coverage of SR1.
  • Each Res is single turn hexagonal copper coil with radius of 1.2 mm, trace width of 100 ⁇ m and thickness of 35 ⁇ m.
  • the final Power Transfer Efficiency (PTEF S) of the pro- posed FS-IPT link is therefore calculated as in equation 7:
  • PTEF S PTE0 ⁇ ⁇ IC ⁇ PTE1
  • ⁇ IC is the efficiency of the IC for switching the operating frequency from the low f0 to the high f 1 .
  • An advantage of the proposed link is physically based on the different frequencies used for the different transmissions.
  • the active resonator is implanted close to the Rx, P3735PC00 / 0013-571 dpt meaning ⁇ 14 mm deep into the head.
  • the invention provides a method for wirelessly powering through induction at least one medical implant configured to be implanted in an organism by receiving power through an implant receiving coil.
  • the method comprises a step of inducing 600 with a transmitter coil that inputs power from a power supply, a first magnetic field 601 at a resonating carrier frequency f0.
  • the method comprises receiving 602 at the first coil the first magnetic field by induction, at the resonating carrier frequency f0 and converting it to an electrical current; operating 603 with the active integrated circuit a frequency change by acting on the electrical current, between the resonating carrier frequency (f0) and a determined frequency (f1); and inducing 604 a second magnetic field 605 in the second coil corresponding to the electrical current at the determined frequency f1.
  • the method then comprises a step of receiving 606 at the implant receiving coil the second magnetic field 605 and converting it into power 607 for the at least one medical implant.
  • the method may further comprise obtaining with the active integrated circuit a frequency change from the resonating carrier frequency (f0) to the determined frequency (f1) by means of a frequency multiplier in case that the determined frequency (f1) is greater or equal to the resonating carrier frequency (f0) or by a frequency divider in case that the determined frequency (f1) is smaller than the resonating carrier frequency (f0).

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  • Engineering & Computer Science (AREA)
  • Health & Medical Sciences (AREA)
  • Power Engineering (AREA)
  • Computer Networks & Wireless Communication (AREA)
  • Animal Behavior & Ethology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Radiology & Medical Imaging (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Biomedical Technology (AREA)
  • Electrotherapy Devices (AREA)

Abstract

L'invention concerne un système de liaison à induction de bobines multifréquence modulaire pour fournir une alimentation sans fil pour au moins un implant médical au niveau d'une sortie d'une bobine de réception, la bobine de réception étant conçue pour être implantée dans un organisme. La liaison à induction à bobines multifréquence modulaire comprend une bobine émettrice conçue pour fourni en entrée de la puissance à partir d'une alimentation de puissance et induire un premier champ magnétique à une fréquence porteuse de résonance. La liaison à induction à bobines multifréquence modulaire comprend en outre un résonateur de déphasage comprenant au moins un circuit intégré actif, une première bobine conçue pour recevoir le premier champ magnétique induit à partir de la bobine émettrice par induction à la fréquence porteuse de résonance et le convertir en courant électrique et une seconde bobine configurée pour transmettre le courant électrique à la bobine réceptrice par induction d'un second champ magnétique à une fréquence déterminée différente de la fréquence porteuse de résonance, le circuit intégré actif étant connecté à la fois à la première bobine et à la seconde bobine et étant conçu pour recevoir la puissance induite à la fréquence porteuse de résonance à travers la première bobine et pour l'utiliser pour piloter une puissance restante réduite en raison d'une dissipation de puissance du circuit intégré actif à la fréquence déterminée à travers la seconde bobine. La bobine réceptrice est conçue pour recevoir la puissance induite par la seconde bobine à la fréquence déterminée et la rendre disponible au niveau de la sortie de la bobine réceptrice.
PCT/IB2023/059962 2022-10-12 2023-10-04 Liaison à induction multifréquence modulaire pour alimenter sans fil de multiples implants miniaturisés Ceased WO2024079570A1 (fr)

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Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20120235502A1 (en) * 2008-09-27 2012-09-20 Kesler Morris P Multi-resonator wireless energy transfer for implanted medical devices
US20170271919A1 (en) * 2016-03-21 2017-09-21 Qualcomm Incorporated Wireless implant powering via subcutaneous power relay
US9991734B2 (en) * 2013-08-19 2018-06-05 Heartware, Inc. Multiband wireless power system
US20220077717A1 (en) * 2020-09-09 2022-03-10 Samsung Electronics Co., Ltd. Apparatus and method with wireless power relay

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20120235502A1 (en) * 2008-09-27 2012-09-20 Kesler Morris P Multi-resonator wireless energy transfer for implanted medical devices
US9991734B2 (en) * 2013-08-19 2018-06-05 Heartware, Inc. Multiband wireless power system
US20170271919A1 (en) * 2016-03-21 2017-09-21 Qualcomm Incorporated Wireless implant powering via subcutaneous power relay
US20220077717A1 (en) * 2020-09-09 2022-03-10 Samsung Electronics Co., Ltd. Apparatus and method with wireless power relay

Non-Patent Citations (11)

* Cited by examiner, † Cited by third party
Title
AHMADI, NUR ET AL.: "2019 9th International IEEEJEMBSConference on Neural Engineering (NER)", 2019, IEEE, article "Towards a distributed, chronically-implantable neural interface"
BARBRUNI GIAN LUCA ET AL: "Miniaturised Wireless Power Transfer Systems for Neurostimulation: A Review", IEEE TRANSACTIONS ON BIOMEDICAL CIRCUITS AND SYSTEMS, IEEE, US, vol. 14, no. 6, 17 November 2020 (2020-11-17), pages 1160 - 1178, XP011836010, ISSN: 1932-4545, [retrieved on 20201231], DOI: 10.1109/TBCAS.2020.3038599 *
BARBRUNI, GIAN LUCA ET AL.: "2021 IEEE International Symposium on Medical Measurements and Applications (MeMeA)", 2021, IEEE, article "A20 Mbps, 433 MHz RF ASKTransmitter to Inductively Power a Distributed Network of Miniaturised Neural Implants"
D. AHNM. GHOVANLOO: "Optimal design of wireless power transmission links for millimetre-sized biomedical implants", IEEETRANS. BIOMED. CIRCUITS SYST, vol. 10, no. 1, February 2016 (2016-02-01), pages 125 - 137, XP011600015, DOI: 10.1109/TBCAS.2014.2370794
G. L. BARBRUNIP. M. ROSD. DEMARCHIS. CARRARAD. GHEZZI: "Miniaturised Wireless Power Transfer Systems for Neurostimulation: A Review", IEEE TRANSACTIONS ONBIOMEDICAL ORCUITS ANDSYSTEMS, vol. 14, no. 6, December 2020 (2020-12-01), pages 1160 - 1178, XP011836010, DOI: 10.1109/TBCAS.2020.3038599
GUIER, ULKUHANYAOYAO JAMAYSAM GHOVANLOO: "A reconfigurable passive RF-to-DCconverter for wireless loTapplications", IEEE TRANSACTIONS ON CIRCUITS ANDSYSTEMS II: EXPRESS BRIEFSQQA, vol. 1, 2019, pages 1800 - 1804
IEEE STANDARDS COORDINATING COMMITTEE: "IEEEstandard for safety levelswith respect to human exposure to radio frequency electromagnetic fields, 3kHz to 300GHz", IEEEC95, 1992, pages 1 - 1991
KHAN SADEQUE REZA ET AL: "Wireless Power Transfer Techniques for Implantable Medical Devices: A Review", SENSORS, vol. 20, 3487, no. 12, 19 June 2020 (2020-06-19), pages 1 - 58, XP093086820, Retrieved from the Internet <URL:https://www.ncbi.nlm.nih.gov/pmc/articles/PMC7349694/pdf/sensors-20-03487.pdf> DOI: 10.3390/s20123487 *
MIRBOZORGI S ABDOLLAH ET AL: "Robust Wireless Power Transmission to mm-Sized Free-Floating Distributed Implants", IEEE TRANSACTIONS ON BIOMEDICAL CIRCUITS AND SYSTEMS, IEEE, US, vol. 11, no. 3, 1 June 2017 (2017-06-01), pages 692 - 702, XP011649785, ISSN: 1932-4545, [retrieved on 20170524], DOI: 10.1109/TBCAS.2017.2663358 *
Q.-A. HUANGL. DONGL.-F. WANG: "LC passive wireless sensors towards a wireless sensing platform: status prospects and challenges", IEEEJ. MICROELECTROMECH. SYST, vol. 25, no. 5, October 2016 (2016-10-01), pages 822 - 841
U.-M. JOWM. GHOVANLOO: "Modelling and optimization of printed spiral coils in air, saline, and muscle tissue environments", IEEE TRANSACTIONSON BIOMEDICAL CIRCUITS AND SYSTEMS, vol. 3, no. 5, 2009, pages 339 - 347

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