Abstract

Dry active electrodes (AE), i.e., the combination of dry electrodes with in situ amplification, are increasingly used for biopotential measurements in emerging healthcare and lifestyle applications [1]. Compared to gel-based wet electrodes, dry electrodes enable fast set-up time, greater user comfort, and long-term monitoring. AE amplifiers ensure local amplification providing improved robustness to noise interference and cable motion artifacts. However, current AEs have analog outputs requiring powerful analog buffers to drive biopotential signals over measurement cables. Furthermore, analog outputs must be digitized by the back-end (BE) system [2,3]. Besides, parameter mismatch between AEs limits the overall CMRR. CMFB [1] or CMFF [2] helps but comes at the expense of increased number cables between the BE and AEs. These problems significantly increase the overall system complexity and cost.

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