electrocardiogram gel electrodes  (LecTec Corporation)

Journal: Nature Electronics

Article Title: Imperceptible augmentation of living systems with organic bioelectronic fibres

doi: 10.1038/s41928-024-01174-4

Figure Lengend Snippet: a , An illustration (top) showing fibres covering the ridges of the fingerprints, where \documentclass[12pt]{minimal} \usepackage{amsmath} \usepackage{wasysym} \usepackage{amsfonts} \usepackage{amssymb} \usepackage{amsbsy} \usepackage{mathrsfs} \usepackage{upgreek} \setlength{\oddsidemargin}{-69pt} \begin{document}$$\frac{N}{d}$$\end{document} N d indicates the number of fibres N across a distance d ; and the experimental evidence is provided by the photographs (bottom row) showing the complete fibre array on a fingertip and the zoom-in view of the fibres follow the ridges of the fingerprints (scale bars left to right, 5 mm, 500 μm). b , Contact impedance versus deposition time on the fingertip. c , Comparison of ECG signals acquired by fibre and gel electrodes at the same time (signal correlation P = 0.99). d , (i) An array of fibres deposited on the thumb muscle region, where ON/OFF loading on the thumb results in clear on/off EMG signals detected by the fibres (scale bar, 1 cm). (ii) Bar chart to depict variations in absolute EMG amplitude from the thumb muscle region against different loading weights on the thumb (data are presented as mean absolute EMG values ± standard deviation of EMG measured for around 5 s in each case). e , Facile repairability of the exposed fibre arrays. The triangular symbol indicates the impedance of the fibre arrays after being deliberately damaged by abrasion, and then new fibres are deposited on demand to repair as indicated by the circular symbols. f , The stability of exposed fibre electrode (exposed bioelectronic fibres on skin) under the conditions of (i) ambient wearing; (ii) mouse clicking; (iii) dry friction wear with a plastic surface (at a surface speed of 4 cm s −1 under around 40% relative humidity (RH) environments); (iv) simulated ‘wet’ conditions without mechanical disturbance. g , Wet friction (at a surface speed of around 4 cm s −1 ) of exposed and cellulose-based fibre protected sensing interface. h , Rinsing under running water (the sensing interface is protected with cellulose-based fibres and the fibre contact is encapsulated with a cellulose-based film) (ECG scales for f , g , horizontal time scale 1 s, vertical voltage scale 0.5 mV). ( a – e , typical results from n = 5 volunteers, f – h , typical results from n = 3 volunteers, for all experiments with n > 3 independent experiments performed on each volunteer).

Article Snippet: The gel electrodes used as references were commercial disposable ECG Electrodes (ADInstruments).

Techniques: Comparison, Standard Deviation

Journal: Nature Electronics

Article Title: Imperceptible augmentation of living systems with organic bioelectronic fibres

doi: 10.1038/s41928-024-01174-4

Figure Lengend Snippet: a , Augmented touch perception via dual-ECG sensing with person-i wearing bioelectronic fibre arrays and person-ii without. The dual-ECG signal acquired through the fibre array is compared with the reconstructed composite-ECG signal from validation gel electrodes. The red downward facing and green upward facing triangles indicate the R peaks of person-i and person-ii, respectively. b , A breathable skin-gated OECT on a fingertip; the OECT displays a response time in the 60 s range. c , Dual-modal sensing for augmented perception of mist pulses with acidic, alkaline and neutral compositions distinguished through colorimetric and electrical readouts. The mist pulse photographs show an example of a neutral mist pulse, and the fibre resistance change was recorded by applying three consecutive neutral mist pulses (normalized resistance change is calculated as \documentclass[12pt]{minimal} \usepackage{amsmath} \usepackage{wasysym} \usepackage{amsfonts} \usepackage{amssymb} \usepackage{amsbsy} \usepackage{mathrsfs} \usepackage{upgreek} \setlength{\oddsidemargin}{-69pt} \begin{document}$$\frac{{R}^{* }-{R}_{0}}{{R}_{0}}$$\end{document} R * − R 0 R 0 , where R* is the peak resistance and R 0 is the initial resistance; the initial resistances of the fibre arrays are in the range of 10 kΩ). a – c , Typical results from n = 5 volunteers, with n > 3 independent experiments performed on each volunteer.

Article Snippet: The gel electrodes used as references were commercial disposable ECG Electrodes (ADInstruments).

Techniques: Biomarker Discovery

Journal: Nature Electronics

Article Title: Imperceptible augmentation of living systems with organic bioelectronic fibres

doi: 10.1038/s41928-024-01174-4

Figure Lengend Snippet: a , An illustration (top) showing fibres covering the ridges of the fingerprints, where \documentclass[12pt]{minimal} \usepackage{amsmath} \usepackage{wasysym} \usepackage{amsfonts} \usepackage{amssymb} \usepackage{amsbsy} \usepackage{mathrsfs} \usepackage{upgreek} \setlength{\oddsidemargin}{-69pt} \begin{document}$$\frac{N}{d}$$\end{document} N d indicates the number of fibres N across a distance d ; and the experimental evidence is provided by the photographs (bottom row) showing the complete fibre array on a fingertip and the zoom-in view of the fibres follow the ridges of the fingerprints (scale bars left to right, 5 mm, 500 μm). b , Contact impedance versus deposition time on the fingertip. c , Comparison of ECG signals acquired by fibre and gel electrodes at the same time (signal correlation P = 0.99). d , (i) An array of fibres deposited on the thumb muscle region, where ON/OFF loading on the thumb results in clear on/off EMG signals detected by the fibres (scale bar, 1 cm). (ii) Bar chart to depict variations in absolute EMG amplitude from the thumb muscle region against different loading weights on the thumb (data are presented as mean absolute EMG values ± standard deviation of EMG measured for around 5 s in each case). e , Facile repairability of the exposed fibre arrays. The triangular symbol indicates the impedance of the fibre arrays after being deliberately damaged by abrasion, and then new fibres are deposited on demand to repair as indicated by the circular symbols. f , The stability of exposed fibre electrode (exposed bioelectronic fibres on skin) under the conditions of (i) ambient wearing; (ii) mouse clicking; (iii) dry friction wear with a plastic surface (at a surface speed of 4 cm s −1 under around 40% relative humidity (RH) environments); (iv) simulated ‘wet’ conditions without mechanical disturbance. g , Wet friction (at a surface speed of around 4 cm s −1 ) of exposed and cellulose-based fibre protected sensing interface. h , Rinsing under running water (the sensing interface is protected with cellulose-based fibres and the fibre contact is encapsulated with a cellulose-based film) (ECG scales for f , g , horizontal time scale 1 s, vertical voltage scale 0.5 mV). ( a – e , typical results from n = 5 volunteers, f – h , typical results from n = 3 volunteers, for all experiments with n > 3 independent experiments performed on each volunteer).

Article Snippet: Individual ECG signals of both people for validation were acquired as references using commercial disposable ECG gel electrodes at the same time (ADInstruments).

Techniques: Comparison, Standard Deviation

Journal: Nature Electronics

Article Title: Imperceptible augmentation of living systems with organic bioelectronic fibres

doi: 10.1038/s41928-024-01174-4

Figure Lengend Snippet: a , Augmented touch perception via dual-ECG sensing with person-i wearing bioelectronic fibre arrays and person-ii without. The dual-ECG signal acquired through the fibre array is compared with the reconstructed composite-ECG signal from validation gel electrodes. The red downward facing and green upward facing triangles indicate the R peaks of person-i and person-ii, respectively. b , A breathable skin-gated OECT on a fingertip; the OECT displays a response time in the 60 s range. c , Dual-modal sensing for augmented perception of mist pulses with acidic, alkaline and neutral compositions distinguished through colorimetric and electrical readouts. The mist pulse photographs show an example of a neutral mist pulse, and the fibre resistance change was recorded by applying three consecutive neutral mist pulses (normalized resistance change is calculated as \documentclass[12pt]{minimal} \usepackage{amsmath} \usepackage{wasysym} \usepackage{amsfonts} \usepackage{amssymb} \usepackage{amsbsy} \usepackage{mathrsfs} \usepackage{upgreek} \setlength{\oddsidemargin}{-69pt} \begin{document}$$\frac{{R}^{* }-{R}_{0}}{{R}_{0}}$$\end{document} R * − R 0 R 0 , where R* is the peak resistance and R 0 is the initial resistance; the initial resistances of the fibre arrays are in the range of 10 kΩ). a – c , Typical results from n = 5 volunteers, with n > 3 independent experiments performed on each volunteer.

Article Snippet: Individual ECG signals of both people for validation were acquired as references using commercial disposable ECG gel electrodes at the same time (ADInstruments).

Techniques: Biomarker Discovery