2021
DOI: 10.1016/j.sbsr.2021.100453
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Nonenzymatic electrochemical sensors via Cu native oxides (CuNOx) for sweat glucose monitoring

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Cited by 21 publications
(35 citation statements)
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“…In the calibration curve shown in Figure 10 B, it can be seen that the sensor exhibits a linear range of up to 2 mM glucose, with R 2 = 0.9979, a sensitivity of 21.02 µA/mM·cm −2 , and a limit of detection (LOD) of 5.2 µM, values calculated based on the 3σ/slope equation, where σ represents the standard deviation of the blank. Actually, the LOD reported in this work is lower than that of other copper-based glucose sensors, such as Cu(II)/rGO/SPCE (65 µM) [ 17 ], Cu nanobelts (10 µM) [ 10 ], Cu-DA (20 µM) [ 39 ], Cu 2 O/PtE (26 µM) [ 40 ], Cu 2 O/Cu microstructures (37 µM) [ 33 ], CuNOx thin films (94.21 µM) [ 41 ], CuO nanowires (10 µM) [ 2 ], CuO nanorods/Nafion/GCE (23 µM) [ 12 ], and CuO nanoplatelets/Nafion/GCE (29 µM) [ 12 ]. Copper-based glucose sensors with an LOD lower than 5.2 µM have been reported in other works [ 9 , 15 , 35 ]; however, more often, their synthesis involves laborious processes and the use of hazardous products or elevated temperatures, not suitable for mass production, compared to DC sputtering, which is a clean and easy-to-scale-up method.…”
Section: Resultsmentioning
confidence: 99%
“…In the calibration curve shown in Figure 10 B, it can be seen that the sensor exhibits a linear range of up to 2 mM glucose, with R 2 = 0.9979, a sensitivity of 21.02 µA/mM·cm −2 , and a limit of detection (LOD) of 5.2 µM, values calculated based on the 3σ/slope equation, where σ represents the standard deviation of the blank. Actually, the LOD reported in this work is lower than that of other copper-based glucose sensors, such as Cu(II)/rGO/SPCE (65 µM) [ 17 ], Cu nanobelts (10 µM) [ 10 ], Cu-DA (20 µM) [ 39 ], Cu 2 O/PtE (26 µM) [ 40 ], Cu 2 O/Cu microstructures (37 µM) [ 33 ], CuNOx thin films (94.21 µM) [ 41 ], CuO nanowires (10 µM) [ 2 ], CuO nanorods/Nafion/GCE (23 µM) [ 12 ], and CuO nanoplatelets/Nafion/GCE (29 µM) [ 12 ]. Copper-based glucose sensors with an LOD lower than 5.2 µM have been reported in other works [ 9 , 15 , 35 ]; however, more often, their synthesis involves laborious processes and the use of hazardous products or elevated temperatures, not suitable for mass production, compared to DC sputtering, which is a clean and easy-to-scale-up method.…”
Section: Resultsmentioning
confidence: 99%
“…Wearable electrochemical sensors for -THC and CBD require further research and development to create POC devices. These devices typically require sensing electrodes, microfluidic and filtering systems, electronics, and wireless communication for data transmission [ 62 , 63 , 64 , 65 , 66 ]. However, integrating all of these components to create small, non-invasive platforms is not easy [ 62 , 65 , 66 , 67 , 68 ].…”
Section: Research Challenges and Future Perspectivesmentioning
confidence: 99%
“…Sweat glucose analysis is probably the most interesting noninvasive method, as it is the base of wearable glucose sensors intended for continuous glucose level monitoring. Alam and Howlader (2021) invented a non-enzymatic glucose sensor based on native copper oxide on copper foil (41). A glucose sensor based on a glassy carbon electrode with low-density polyethylene and covalently immobilized glucose oxidase was designed for the analysis of sweat glucose by Fabregat and co-authors (2021) (42).…”
Section: Non-invasive and Portable Glucose Biosensorsmentioning
confidence: 99%