fig1

Figure 1. Design principle and representative applications of SIRES for wearable and implantable molecular monitoring. (A) Core design concept and cross-sectional schematic of the fully elastomeric trilayer SIRES architecture, comprising an SRC for stable electron transport, an ETI for regulating strain-dependent electrochemical coupling, and an SFC for stabilizing bioactive sensing elements; (B and C) Modified Randles-equivalent-circuit model and relative resistance changes under strain, showing how strain-induced resistance increases are balanced by electrochemically active surface-area modulation; (D) Wireless sweatband implementation for multiplexed sweat monitoring with mobile readout. Scale bar, 5 mm; (E) Implantable SIRES bioelectronics mounted on the rat stomach for gastric glucose monitoring. (A-E) Reprinted in part with permission from^[15]. Copyright 2026, AAAS; (F) Viewpoint of this Commentary. Organ deformation (1) alters the electrochemical reaction at the interface (2), and the resulting error is corrected at two levels that operate on different timescales. At the device level, the strain-dependent rise in ETI resistance is matched to the area-driven fall in R_ct, so the deviation is canceled as it arises (3.1 and 4.1). At the computational level, an AI-assisted model addresses residual error and slowly accumulating drift, and indicates when recalibration is required (3.2 and 4.2), together sustaining stable quantitative measurement (5). SIRES: Intrinsically stretchable interface for resilient electrochemical sensing; SRC: strain-resilient conductor; ETI: electrically tunable interface; SFC: stretchable functional coating; R_ct: charge-transfer resistance; WPU: waterborne polyurethane; CNTs: carbon nanotubes; LM: liquid metal; PU: polyurethane; VIA: vertical interconnect access.