“…When SW 1 is off, the stored current (i L2 ) in the L 2 C 2 tank charges C LV1 or C LV2 . During this phase, V CP instantly changes from 0 to either V LV1 or V LV2 , same as the in-phase current mode of the work with commercial-off-the-shelf (COTs) components in [52]. When V LV1 and V LV2 reach the target regulating voltages (4.7/2 V), switching pulses are skipped for voltage regulation.…”
Single modality wireless power transfer has limited depth for mm-sized implants across air/tissue or skull/tissue interfaces because they either suffer from a high loss in tissue (RF, optical) or high reflection at the medium interface [ultrasound (US)]. This article proposes an RF-US relay chip at the media interface avoiding the reflection at the boundary and enables efficient wireless powering to mm-sized deep implants across multiple media. The relay chip rectifies the incoming RF power through an 85.5% efficient RF inductive link (across air) using a multi-output regulating rectifier (MORR) with 81% power conversion efficiency (PCE) at 186 mW load and transmits using adiabatic power amplifiers (PAs) to the implant in order to minimize cascaded power loss. To adapt US focus to implant movement or placement, beamforming was implemented using six channels of US PAs with two-bit phase control (0 • , 90 • , 180 • , and 270 • ) and three different amplitudes (6-29, 4.5, and 1.8 V) from the MORR. The adiabatic PA contributes a 30%-40% increase in efficiency over class-D and beamforming increases the efficiency by 251% at 2.5 cm over fixed focusing. The proof-ofconcept powering system for a retinal implant, from an external PA on a pair of glasses to a hydrophone with 1.2 cm (air) + 2.9 cm (agar eyeball phantom in mineral oil) separation distance, had a power delivered to the load (PDL) of 946 µW. The 2.3 mm × 2 mm relay chip was fabricated in a 180 nm highvoltage (HV) BCD process. Index Terms-Adiabatic power amplifier (PA), beamforming, implantable medical device (IMD), in-depth powering, inductive powering, multi-output regulating rectifier (MORR), phased array, power relay, retinal implant, ultrasonic power transfer, wireless power transfer.
“…When SW 1 is off, the stored current (i L2 ) in the L 2 C 2 tank charges C LV1 or C LV2 . During this phase, V CP instantly changes from 0 to either V LV1 or V LV2 , same as the in-phase current mode of the work with commercial-off-the-shelf (COTs) components in [52]. When V LV1 and V LV2 reach the target regulating voltages (4.7/2 V), switching pulses are skipped for voltage regulation.…”
Single modality wireless power transfer has limited depth for mm-sized implants across air/tissue or skull/tissue interfaces because they either suffer from a high loss in tissue (RF, optical) or high reflection at the medium interface [ultrasound (US)]. This article proposes an RF-US relay chip at the media interface avoiding the reflection at the boundary and enables efficient wireless powering to mm-sized deep implants across multiple media. The relay chip rectifies the incoming RF power through an 85.5% efficient RF inductive link (across air) using a multi-output regulating rectifier (MORR) with 81% power conversion efficiency (PCE) at 186 mW load and transmits using adiabatic power amplifiers (PAs) to the implant in order to minimize cascaded power loss. To adapt US focus to implant movement or placement, beamforming was implemented using six channels of US PAs with two-bit phase control (0 • , 90 • , 180 • , and 270 • ) and three different amplitudes (6-29, 4.5, and 1.8 V) from the MORR. The adiabatic PA contributes a 30%-40% increase in efficiency over class-D and beamforming increases the efficiency by 251% at 2.5 cm over fixed focusing. The proof-ofconcept powering system for a retinal implant, from an external PA on a pair of glasses to a hydrophone with 1.2 cm (air) + 2.9 cm (agar eyeball phantom in mineral oil) separation distance, had a power delivered to the load (PDL) of 946 µW. The 2.3 mm × 2 mm relay chip was fabricated in a 180 nm highvoltage (HV) BCD process. Index Terms-Adiabatic power amplifier (PA), beamforming, implantable medical device (IMD), in-depth powering, inductive powering, multi-output regulating rectifier (MORR), phased array, power relay, retinal implant, ultrasonic power transfer, wireless power transfer.
“…The main aim of [29] is to suggest a soft switching inverter with WPT application; however, load and MI changes, misalignment, and frequency modulation have not been considered. The literature [30] has proposed a new multi-phase structure for WPT. Although using a multi-phase rectifier has improved the power transfer rate, poor coil coupling has limited the application of [30] in low power implementation.…”
Section: Introductionmentioning
confidence: 99%
“…The literature [30] has proposed a new multi-phase structure for WPT. Although using a multi-phase rectifier has improved the power transfer rate, poor coil coupling has limited the application of [30] in low power implementation. In [31], a maximum efficiency point tracking algorithm has been suggested for a DWPT converter where the wireless communication between the sender and receiver has increased cost and restricted its application in noisy enlivenments.…”
This paper offers a new EF-class converter for dynamic wireless power transfer application. The proposed high-frequency converter employs a floating-frequency switching algorithm to control the converter in a continuous frequency range, eliminate the requirement to any additional operational data from the secondary (receiver) side, accelerate the load impedance match while moving, maximize the transferred power rate, reduce charging interval and compensate power transfer tolerances. Moreover, an optimized super elliptical shape coil is designed to cope with lateral misalignment, enhance coil coupling, and increase efficiency. In the proposed converter, (i) soft switching is implemented to increase switching frequency, decrease passive components size, and improve power density, (ii) undesired voltage harmonics are attenuated to reduce peak voltage stress of the power switch in a wide frequency range, (iii) the receiver side is enabled for higher mobility with stable power transfer, and (iv) the resonant frequency is updated to compensate non-accurate values of passive components in experimental prototyping. In this study, the operational analytics, compensation method, control algorithm, coil design and converter optimization are followed with some comparisons to present the converter capabilities. In addition, simulation and experimental results are provided under different degrees of misalignment to verify the accuracy of theoretical analytics.INDEX TERMS EF-class resonant converter, floating-frequency switching algorithm, coil shape optimization, dynamic wireless power transfer.
“…A robust selfregulated rectifier without any switching circuitry is proposed for biomedical devices [10]. In [11], a multi-phase resonancebased boosting rectifier is presented to power different loads. However, the circuit configuration at the Rx side is complex and the power transfer capability is limited [10], [11].…”
Section: Introductionmentioning
confidence: 99%
“…In [11], a multi-phase resonancebased boosting rectifier is presented to power different loads. However, the circuit configuration at the Rx side is complex and the power transfer capability is limited [10], [11].…”
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