Electrical communication between an enzyme and an electrode is one of the most important factors in determining the performance of biofuel cells. Here, we introduce a glucose oxidase-coated metallic cotton fiber-based hybrid biofuel cell with efficient electrical communication between the anodic enzyme and the conductive support. Gold nanoparticles are layer-by-layer assembled with small organic linkers onto cotton fibers to form metallic cotton fibers with extremely high conductivity (>2.1×104 S cm−1), and are used as an enzyme-free cathode as well as a conductive support for the enzymatic anode. For preparation of the anode, the glucose oxidase is sequentially layer-by-layer-assembled with the same linkers onto the metallic cotton fibers. The resulting biofuel cells exhibit a remarkable power density of 3.7 mW cm−2, significantly outperforming conventional biofuel cells. Our strategy to promote charge transfer through electrodes can provide an important tool to improve the performance of biofuel cells.
Biofuel cells (BFCs)1 are thought to be one of the most attractive power sources for implantable and microscale biomedical devices because of their biocompatibility and operation at mild temperatures and near-neutral pH2,3,4. Despite these advantages, the relatively low power output of BFCs compared to other power sources, resulting from slow electron transfer, poor utilization efficiency of the enzyme, and limited mass transport, has restricted their practical applications. In particular, poor electrical communication between the enzyme and the conductive support has a critical effect on the power output of BFCs5,6. To overcome this problem, redox mediators between the enzyme and the conductive support have been introduced to improve the electrical communication between the two, thereby enhancing the power performance of the cell. To the best of our knowledge, the best power performance reported to date for these mediated electron-transfer-based BFCs (MET-BFCs) is 2.18 mW cm−2 7. However, the incorporation of a redox mediator in BFCs can lead to several issues, such as toxicity, instability, the complex synthesis of redox mediators, and a reduced open-circuit voltage. Thus, recent research efforts have focused on the development of direct electron transfer-based BFCs (DET-BFCs) with improved performance8.
A variety of conductive carbon materials (e.g., carbon nanotubes (CNTs)9,10,11, graphene12, and porous carbon13) with large surface areas, 3D porous structures for facile mass transport, and high electrical conductivities (<300 S cm−1) have been proposed as supports having favorable electrical communication with the enzyme layer. For example, Zebda et al. demonstrate that DET-BFCs based on CNT supports exhibited a significantly higher power output of 1.25 mW cm−2 compared to previously reported DET-BFCs fabricated by solution drop casting and high mechanical compression5. Despite all the merits of the carbon substrates for the BFCs, their biosafety for long-term operation in the in vivo systems is still controversial due to the cellular toxicity nature14,15. Furthermore, in most cases, the enzymes have been directly deposited onto these carbon supports through conventional physical adsorption, which has limitations in terms of the precise control of the interfacial distance, conformation, and stability between the enzyme and the conductive support, resulting in poor utilization of the enzymes for catalyzing electrochemical reactions.
With the advances of the anode for the glucose oxidation reaction through glucose oxidase (GOx), the proper design of the cathode to improve the oxygen reduction reaction (ORR) activity is also crucial to obtain the high-power density and efficiency. In this regard, the cathodic enzyme, such as laccase or bilirubin oxidase, have been intensively studied due to their excellent ORR activity5,16. However, the catalytic activity and stability are strongly dependent on the physiological conditions of the mammal’s body fluid such as pH, temperature, and chlorine concentration17,18,19,20. As an alternative, catalytic metal nanoparticles (NPs) such as Pt, Pd, and Au with high ORR activity have been considered as the competent candidates to the abiotic ORR catalysts21,22. Despite the improved performance, conventional methods of depositing NPs onto the substrates, such as the mixing of NPs with carbon-substrates23 or chemical reduction of the metal precursor, etc.22,24 have poor controls over the structures of NPs on the substrates. In addition, chemical reduction methods often cause particle agglomeration between adjacent NPs with the reduced electrochemical surface area, which hinders high mass loading of NPs on the substrates25. Therefore, it is ideal to incorporate the catalytic NPs onto the substrates in a controlled, 3D spatial arrangement without agglomeration, which can facilitate electron and ion transport for the efficient electrocatalytic reaction.
Layer-by-layer (LbL) assembly methods offer effective opportunities to prepare enzymatic or conductive multilayer films with tailored thickness, functionalities, and composition on substrates of various sizes and shapes utilizing complementary interactions26,27,28,29,30,31,32,33,34,35,36,37,38. However, as bulky insulating polyelectrolytes are generally LbL-assembled with the desired functional components (e.g., metal NPs, enzymes, functional polymers39) to build up multilayers, the mutual electron transfer is significantly suppressed due to the increased contact resistance40. Therefore, the ideal LbL assembly for BFC applications should replace bulky polymer electrolytes with small-molecule linkers that can facilitate the electrical communication between the active materials as well as enable the efficient assembly of the catalysts with a controlled structure and loading amount.
Here, we introduce a highly porous metallic cotton fiber-based BFC (MCF-BFC) fabricated using small-molecule linker-induced LbL assembly of the active catalysts, which significantly boosts the DET rate between the enzymes and the conductive supports (Fig. 1). In particular, the Au NPs are selected to fabricate the MCF because of their several benefits in electrochemical biomedical fields41, such as the superior biocompatibility42, more facile surface modification43, and higher electrical conductivity. In this case, the MCFs act as not only the conductive host for depositing the anodic enzyme materials, but also the electrocatalytic cathode for ORR. More importantly, it is worth noting that the loading amount of the metal NPs in the MCF can be easily increased forming the 3D porous structure according to the increase of the bilayer number, and thereby achieving both the higher electrical conductivity and the improved ORR activity without cathodic enzymes. As a result, our hybrid MCF-BFC provides a remarkable power density of 3.7 mW cm−2 using a fixed external resistance without the aid of redox mediators, significantly exceeding the power density of the previously reported conventional DET- and MET-BFCs.
For the fabrication of the MCF, instead of bulky polymers such as polyelectrolytes, we employ an amine-functionalized small molecule, tris-(2-aminoethyl)amine (TREN), that can electrostatically interact with GOx as well as covalently interact with Au NPs. First, LbL assembly of TREN and tetraoctylammonium bromide-stabilized Au NPs (TOA-Au NPs) was carried out on cotton fibers. In this case, the amine groups of TREN can covalently adsorb on the surface of Au NPs due to its stronger affinity than the ammonium group of TOA. Then, negatively charged GOx was electrostatically LbL-assembled onto the TOA-Au NP/TREN multilayer-coated cotton fibers using positively charged TREN in water. Based on this unique LbL assembly of conductive NPs and enzyme materials through the same small-molecule linker allowing different interactions, we fabricate entirely different MCF electrodes that have extremely high electrical conductivity (>2.1×104 S cm−1) and yet still maintain the intrinsic 3D porous structure of cotton fibers with conformal coatings of the active layers. With its extremely high electrical conductivity and highly porous 3D structure, MCF can facilitate charge transfer to the conformally coated enzyme layers as well as the mass transport of glucose (for oxidation by GOx) and oxygen (for reduction by Au NP) through the electrodes, thus enabling effective electrocatalytic reactions. Furthermore, the robust covalent bonding between the Au NPs and TREN and the electrostatic bonding between GOx and TREN increase the operational stability of the MCF-BFCs. Given that these unique characteristics of MCFs play a decisive role in enhancing the power output of hybrid BFCs, this approach can contribute to the design of other high-performance electrodes for various electrochemical applications, including other energy storage devices and sensors.
Performance of metallic cotton fiber cathodes
For the preparation of the MCF electrode, TOA-Au NPs with a diameter of 8 nm43 were LbL-assembled with TREN onto a cotton fiber composed of multiple hydrophilic microfibrils (cellulose fibers containing hydroxy groups). The TOA-Au NPs were uniformly and densely coated onto all the microfibrils that make up the cotton fiber (~200 μm diameter) without disrupting the inherently porous structure (Fig. 2a, b and Supplementary Fig. 1). This was confirmed by field-emission scanning electron microscopy (FE-SEM), energy-dispersive X-ray spectroscopy (EDS) mapping, and topographic atomic force microscopy (AFM) (Fig. 2c and Supplementary Fig. 2). It is worth noting that the amount of (TOA-Au NP/TREN)n multilayers loaded onto the porous cotton fibers (8.5 mg cm−2 for n = 20) was more than ten times higher than that loaded onto nonporous nylon fiber, which has the same dimension (~200-μm-diameter) as a cotton fiber (0.8 mg cm−2 for n = 20) (Fig. 2d and Supplementary Fig. 3). The electrical conductivity and resistivity of the MCF showed strong correlations with the number of bilayers; a high conductivity of ~3.5×103 S cm−1 and a low resistivity of ~1.2×10−4 Ω cm were measured for (TOA-Au NP/TREN)20 multilayers (Fig. 2e). This correlation indicates that the electrical properties of the MCFs with higher loading are closer to those of bulk Au wire (electrical conductivity ~4.1×105 S cm−1, resistivity ~2.1×10−6 Ω cm). It should be noted that the conductivity of bare CNT fibers does not exceed 600 S cm−1 without additional post-treatment44,45. Furthermore, the formed MCF retains its intrinsic flexibility even though Au NPs are densely loaded onto the bare cotton fiber (Supplementary Fig. 4).
The high electrical conductivity of MCFs is caused by the unique adsorption mechanism, in which the bulky and hydrophobic TOA ligands of the TOA-Au NPs are sequentially replaced by small TREN ligands containing amine (NH2) groups during the LbL assembly. As confirmed by Fourier transform infrared (FTIR) spectroscopy (Fig. 2f and Supplementary Fig. 5), the first deposition of TOA-Au NPs onto a poly(ethylenimine) (PEI, Mw ~800)-coated Si wafer (i.e., 0.5 bilayer) generated the characteristic peaks of TOA ligands (C−H stretching vibrations at 2928 and 2856 cm−1) and the amine groups of PEI (N−H bending at 1654 and 1554 cm−1). The subsequent adsorption of TREN onto the outermost TOA-Au NP layer (i.e., 1 bilayer) eliminated the C−H stretching peaks corresponding to the TOA ligands with long alkyl chains, while the N−H bending peaks were intensified by TREN adsorption. As a result, this sequential ligand exchange reaction allows TREN to act as a new molecular linker between adjacent Au NPs instead of the bulky TOA ligands, which minimizes the distance and contact resistance between the Au NPs.
We also investigated the electrochemical properties of the (TOA-Au NP/TREN)n-coated cotton fiber electrodes (hereafter abbreviated as n-MCF) as a function of the number of bilayers (n) at a scan rate of 5 mV s−1 using a three-electrode cell configuration in 20 mmol L−1 phosphate-buffered saline (PBS) solution under ambient conditions. Cyclic voltammetry (CV) scans showed a gradual increase in cathodic current densities when the number of bilayers (n) was increased from 5 to 20 due to the increased active surface area from the introduced Au NPs46 (Fig. 2g) (please note that the power density of MCF-based hybrid BFCs was evaluated by measuring the current output applying a fixed external resistance to eliminate the capacitive and other parasite currents). Additionally, electrochemical impedance spectroscopy (EIS), obtained from the fitting of the Randle’s equivalent circuit, also demonstrated the improved electrical conductivity of 20-MCF, with significantly decreased equivalent series resistance (ESR) of 30 Ω (at 1 kHz) and charge transfer resistance (Rct) of 4 Ω relative to those of the 5-MCF electrode (ESR ~1346 Ω and Rct ~303 Ω; Fig. 2h, Supplementary Fig. 6a, and Supplementary Note 1). These results clearly show that the electrochemical properties of MCF electrodes are governed by the Au NP loading47, which can be further improved by increasing the number of bilayers. In addition, the very high knee frequency of 20-MCF (119.4 Hz) compared to 5-MCF (10.9 Hz) indicates better mass transport for the highly porous structure with sufficient Au NP coverage (Supplementary Fig. 6b). Therefore, an n-MCF electrode can provide bilayer-dependent electrocatalytic activity toward the ORR as a cathode, and it can also be used as a host for the anode (ultimately, for a complete hybrid BFC).
To confirm these possibilities, we further investigated the electrochemical cathodic properties of MCFs using CV in oxygen-free (N2), ambient, and oxygen-rich PBS solutions (Supplementary Fig. 7a, b). The measured cathodic current densities of the 20-MCF electrode in ambient and O2 conditions at a potential of −0.6 V were found to be −17.1 and −27.9 mA cm−2, respectively. The normalized current density levels were obtained by subtracting the areal cathodic current density level measured at a specific potential of −0.6 V in oxygen-free condition from the areal cathodic current density level measured at the same potential in ambient or oxygen-rich condition. On the basis of −7.1 mA cm−2 in oxygen-free N2 condition, the normalized cathodic current densities at −0.6 V were −10 mA cm−2 (with an ESR of 33 Ω) under ambient condition, and −20.7 mA cm−2 (with an ESR of 29 Ω) under O2 condition (Supplementary Fig. 7c, d).
In addition, it should be noted that the measured cathodic current density (−17.1 mA cm−2) for the 20-MCF electrode outperforms the current density level (−3.0 mA cm−2) of nonporous bulk Au wire with the same diameter in ambient conditions (Supplementary Fig. 8). This remarkable cathodic behavior of an MCF electrode is caused by the extremely large surface area of the electrocatalytic Au NP-based MCF, which arises from the microporous structure of the cotton fibrils as well as the nanoporous structure of the Au NP multilayers.
Performance of glucose oxidase/metallic cotton fiber anodes
We prepared MCF-based anodes through the additional deposition of electrostatically LbL-assembled (anionic GOx/cationic TREN) multilayers onto 20-MCF in PBS solution. In this process, GOx, with an isoelectric point of pH 4.3, has a net negative charge in pH 7.4 PBS solution, which can induce the electrostatic adsorption of positively charged TREN molecules (having protonated amine groups NH3+ at pH 7.4). The LbL-assembled GOx can catalyze the oxidation of glucose to gluconolactone, and the electrons generated can be directly transferred from the enzyme to the MCF electrode (Fig. 3a). First, the LbL assembly behavior of the (GOx/TREN)m (where m is the number of bilayers) multilayers on (TOA-Au NP/TREN)-coated quartz glass was investigated by ultraviolet-visible (UV−Vis) spectroscopy (Fig. 3b and Supplementary Fig. 9). In this case, we observed linear hyperchromism at 277 nm associated with the oxidized flavin cofactors of GOx as a function of m, implying the uniform and sequential formation of GOx/TREN multilayers (the inset of Fig. 3b). This growth behavior was further quantitatively monitored using a quartz crystal microbalance (QCM). The increase in frequency changes (−ΔF) or the decrease in mass changes (ΔM) after deposition of each TREN layer can be attributed to the partial desorption of weakly adsorbed GOx during the adsorption of TREN (Supplementary Fig. 10). Additionally, the film thickness of the formed (GOx/TREN)m multilayers, which are sequentially deposited with small-molecule linkers instead of conventional bulky polyelectrolytes35,36,37, was estimated to be ~9 ± 3 nm and ~13 ± 5 nm for 20 and 30 bilayers, respectively (Supplementary Fig. 11). Considering the dimension of GOx (6.0 nm × 5.2 nm × 7.7 nm)48, these multilayer thicknesses indicate that (GOx/TREN)20 and (GOx/TREN)30 are adsorbed on the substrates like a single GOx layer and double GOx layers, respectively. As a result, the adsorption conformation of thin and uniform (GOx/TREN)m multilayers can facilitate the electron transfer through the enzyme layers.
We also examined the glucose electrooxidation activity of the anode as a function of m in PBS solution containing glucose (300 mmol L−1) at a scan rate of 5 mV s−1 (Fig. 3c and Supplementary Fig. 12). The CVs of the (GOx/TREN)m multilayer-coated 20-MCF electrode (hereafter abbreviated as m-GOx/20-MCF) showed that the overall current density of the electrode steadily increased with increasing number of bilayers (m) from 0 to 30. This bilayer (m)-dependent anodic performance can be explained by different adsorption behavior of the GOx layer on the inner and outer surface of the MCFs. In other words, in the case of the GOx/TREN multilayers onto the interior of highly porous MCFs, it is considered that their thicknesses will be much thinner with going from the outer surface to the center region of MCFs because the repetitive deposition of bulky GOx layers can block up the porous structure of MCFs. Therefore, the overall anodic current density of MCF-based anode electrode can be gradually increased up to the thickness of GOx/TREN multilayers allowing efficient electron tunneling. The anodic current density level measured at +0.6 V approached a maximum value of ~50 mA cm−2 (the normalized anodic current density level at +0.6 V was ~40 mA cm−2, the inset of Fig. 3c) after the deposition of 30 bilayers.
In this case, the 30-GOx/20-MCF anode maintained ~97.5% of its initial current density after continuous operation for 1 h (herein, the initial current density of the anode electrode was obtained after pretraining for 1 day in 300 mmol L−1 glucose containing PBS buffer condition), indicating the excellent electrode stability caused by the precisely controlled deposition of GOx using TREN (Supplementary Fig. 13). Conversely, the ESR value slightly increased with increasing m, indicating an increase in the internal resistance, corresponding to the increased loading amount of insulating GOx/TREN multilayers onto 20-MCF (Fig. 3d). However, the ESR value of the MCF-based anode electrode is much lower than that of the nonporous electrode (i.e. Au-coated Si wafer-based anode) (Supplementary Fig. 14) although the loading amount of (GOx/TREN)30 multilayers onto MCF electrode is 185 times higher than that of (GOx/TREN)30 multilayers onto nonporous electrode (i.e., ~860 μg cm−2 for MCF-based anode and ~4.65 μg cm−2 for nonporous substrate-based anode at 30 bilayers), which indicate the effective electrode conformation of the MCF-based anode for facile electrochemical kinetics.
We also observed that the electron transfer kinetics at the interface of the electrode are significantly influenced by a kind of outermost layer of GOx/TREN multilayers (Supplementary Fig. 15). More specifically, OH-functionalized glucose has a higher affinity (mainly, hydrogen-bonding interaction) with amine-functionalized TREN than negatively charged GOx at pH 7.4 (due to the presence of carboxylate ion (COO−) groups of GOx). In line with this high affinity, glucose could be easily diffused into the outermost TREN-coated multilayer films, and therefore the outermost TREN-coated electrode exhibited much lower electron transfer resistance than the outermost GOx-coated electrodes in spite of the increase of layer number. These similar phenomena were also demonstrated by Willner group49. Considering that all the BFCs shown in our study are based on the outermost TREN-coated electrodes as well as the highly porous electrodes, the electron transfer resistances of MCF-based electrodes can be significantly lowered compared to those of other nonporous electrodes.
Furthermore, we investigated the oxidation activity of the (GOx/TREN)30 electrode when the glucose concentration in the PBS solution was increased from 0 to 300 mmol L−1 in PBS solution (Supplementary Fig. 16). The anodic current density measured at +0.6 V reached a saturated level at 300 mmol L−1 glucose, revealing the Michaelis–Menten-type behavior50 of the GOx (the inset of Supplementary Fig. 16b). In this case, the normalized anodic current density of the electrode increased to ~40 mA cm−2 at a glucose concentration of 300 mmol L−1, showing a high electrooxidation reaction involving GOx on the MCF without additional redox mediators. Additionally, a linear dependence of the normalized current densities on the low glucose concentration ranging from 0 to 300 mmol L−1 suggests the possibility that the (GOx/TREN)m–coated electrodes can be also used as in vivo glucose sensors (Supplementary Fig. 16d). We also found that the Au NPs on cotton fibers can catalyze the electrooxidation of glucose in aqueous electrolytes51, generating the anodic current without GOx. In the case of GOx-free MCFs, the anodic current density was gradually increased with increasing the concentration of glucose in PBS, which corresponds to approximately 22% of the anodic performance of 30-GOx/20-MCF (Supplementary Fig. 17). These results indicate that the highly porous MCFs can serve as a promising host for effective loading of the enzyme catalyst (GOx) as well as the co-catalyst for the oxidation of glucose. Particularly, it should be here noted that these high electrocatalytic activities of the highly porous (GOx/TREN)m electrodes are in stark contrast to those of nonporous substrate-based electrodes. When the (GOx/TREN)m multilayers were deposited onto (TOA-Au NP/TREN)20 multilayer-coated Si wafers, the (GOx/TREN)10-coated flat substrate anode in a 300 mmol L−1 glucose solution exhibited a maximum normalized current density level of ~0.01 mA cm−2 at +0.6 V (Supplementary Fig. 18).
In addition to the highly porous structure, the excellent electrical conductivity of MCFs also plays an important role on the anode performance. To verify the effect of the electrical conductivity on the catalytic properties of anode electrodes, we further investigated the electrochemical properties for two different kinds of MCFs with different electrical conductivities. For demonstrating this issue, the (TOA-Au NP/PEI)20-coated cotton fiber (i.e. PEI-MCF) was prepared as a comparison target of the (TOA-Au NP/TREN)20-coated cotton fiber (i.e. TREN-based MCFs). In this case, the PEI-based MCF showed an extremely low electrical conductivity of ~0.02 S cm−1 compared to that of the TREN-based MCF (~3.5×103 S cm−1) due to the use of bulky insulating PEI (Mw~25,000) despite their similar physical characteristics such as total thickness and surface morphology (Supplementary Fig. 19). Then, the (GOx/TREN)20 multilayers were sequentially deposited onto these MCFs. Although the same layer number (or mass) of GOx was immobilized onto each MCF (i.e. PEI- and TREN-based MCFs), the electrooxidation response of the PEI-based MCF anode was significantly low compared to that of the TREN-based MCF (Supplementary Fig. 20), which mainly originated from the poor electron and mass transfer efficiency of PEI-based MCF52. These results clearly imply that the highly conductive and porous TREN-based MCF can be used as an effective host for GOx.
To further investigate the catalytic kinetics of 30-GOx/20-MCF (hereafter, 20-MCF means TREN-based 20-MCF) anode, the apparent heterogeneous electron transfer rate (Ks) was estimated using the Laviron method53 for a surface-controlled electrochemical system (Supplementary Fig. 21). In this case, Ks of the electrode was obtained by using the plot of potential (E−E0) vs. scan rate (log v), which was recorded from the CV data. As a result, the 30-GOx/20-MCF anode exhibited a relatively large Ks value of 6.0 ± 0.1 s−1 and a small redox peak potential separation (∆Ep) of 60 mV at a scan rate of 100 mV s−1. Here, small ∆Ep (60 mV at a scan rate of 100 mV s−1) indicates fast heterogeneous electron transfer process, and the reaction is not a diffusion-controlled process but a surface-controlled one, as expected for immobilized system (more specifically, in the case of the surface-controlled system, ΔEp is less than 200 mV54). Additionally, a large ks of 6.0 ± 0.1 s−1 obtained from 30-GOx/20-MCF suggests that the electrode is significantly effective in facilitating the direct electron transfer of GOx55,56,57. As a result, the formed 30-GOx/20-MCF electrode provides efficient catalytic kinetics with smaller ∆Ep and larger ks (for example, 1.53 s−1 for multi-walled carbon nanotubes (MWNT)-modified electrode, 0.3 s−1 for single-walled carbon nanotubes (SWNT)-modified electrode, 3.96 s−1 for the porous TiO2 electrode, and 6.28 s−1 for GOx-carbon nanodots on the glassy carbon electrode)58.
We also highlight that the use of a small-molecule linker between neighboring enzymes can allow facile charge and/or mass transport through the enzyme layer. For comparison between small-molecule and polymer linkers, GOx was electrostatically LbL-assembled with PEI (Mw ~25,000), a bulky polymer linker, onto 20-MCF for the preparation of (GOx/PEI)30/20-MCF electrodes (Fig. 4a). In this case, not only the nanopores but also the micropores in the micro-fibril structure of the MCF-based electrode disappeared with the deposition of (GOx/PEI)30 multilayers (Supplementary Figs. 22 and 23). As a result, the electrochemical performance of the (GOx/PEI)30/20-MCF electrode was lower (i.e. a low anodic areal current density, a high internal resistance and a low ion-diffusion rate) than the (GOx/TREN)30/20-MCF (i.e., 30-GOx/20-MCF) electrode (Fig. 4b, c, Supplementary Figs. 24 and 25), further confirming the role of the small-molecule linker. This conformal coating of the thin GOx layer on the conductive MCF facilitates charge transfer and thereby maximizes the catalytic reaction of GOx. Additionally, we expect that the anodic performance can be further controlled and enhanced with increasing the electrical conductivity of MCF for facile electrical communication and the surface area of MCF for efficient enzyme loading (by a further increase (i.e., n > 20) of bilayer number of (TOA-Au NP/TREN)n multilayers onto cotton fibers).
Performance of hybrid metallic cotton fiber-biofuel cells
To demonstrate a working MCF-BFC, the 30-GOx/20-MCF anode was connected to the 20-MCF cathode and the power density was evaluated by measuring the current flow through a fixed external resistance in the range of 1 kΩ−10 MΩ without membrane (Supplementary Fig. 26a). The resulting MCF-BFC delivered the maximum areal power density of approximately 1.4 mW cm−2 at the potential of +0.37 V in the electrolyte containing 300 mmol L−1 glucose under ambient condition (Supplementary Fig. 26b). Although the power density at the lower concentration of 10 mmol L−1 was decreased to ~0.9 mW cm−2, this performance was still sufficiently high to support various in vivo applications59, such as self-powering glucose sensors60 or implantable power supplies for cardiac pacemaker61, neurostimulator62, and drug pumps63. The MCF-BFC also exhibited high operational stability, maintaining ~71% (~0.6 mW cm−2) of its initial power density and voltage retention of ~83% after continuous operations for 20 days (~62% of the initial power density and voltage retention of ~79% after 35 days) (Supplementary Fig. 26c, d).
Power output enhancement of hybrid metallic cotton fiber-biofuel cells
The power output of MCF-BFCs can be further improved by enhancing the active surface area and electrical conductivity of the cathode electrode. We systematically controlled the number of bilayers (n) of (TOA-Au NP/TREN)n from 20 to 120 in the cathode and investigated its effect on the power performance of MCF-BFCs (Fig. 5a). Through this process, the electrical conductivity of n-MCFs increased to approximately 2.1×104 S cm−1 (Au NP/TREN loading density of ~51.7 mg cm−2) at n = 120 (Supplementary Fig. 27). At a potential of −0.6 V, the cathodic current density gradually increased from −17 mA cm−2 for 20-MCF to −38 mA cm−2 for 120-MCF (Fig. 5b and Supplementary Fig. 28). Additionally, the ORR peaks progressively shifted to positive potentials with an increasing number of bilayers, which can be attributed to the increased electrical conductivity and decreased overpotential for the ORR64. This was further confirmed by the decreased ESR values of n-MCFs from approximately 24 to 13 Ω as n was increased (Fig. 5c). The assembled cathodes with different numbers of bilayers were connected to a constant anode (i.e., 30-GOx/20-MCF) with an external resistor for the preparation of complete BFCs. The maximum areal power densities were found to increase gradually with the number of bilayers of the cathode (Fig. 5d and Supplementary Fig. 29). As a result, our MCF-BFC composed of a 120-MCF cathode and a 30-GOx/20-MCF anode (i.e. 120-MCF-BFC) exhibited the maximum areal power density of 3.7 mW cm−2 in 300 mmol L−1 glucose under ambient condition applying a fixed external resistance, considerably outperforming conventional BFCs (including MET-BFCs) reported to date (Supplementary Table 1). This high-power output (3.7 mW cm−2) obtained from our membrane-free and mediator-free MCF-BFC is in stark contrast with those measured from other mediator-free enzymatic fuel cells (i.e. in the case of being measured by an external resistor, the power output of mediator-free enzymatic fuel cells is generally less than ~1 mW cm−2). For example, the power output shown in our system is nearly three times higher than that of the previous DET-based compressed CNT electrode5 (1.25 mW cm−2, measured by polarization tests, i.e. CV measurements, without an external resistor), and even higher than that of the reported osmium complex-based bi-scrolled carbon nanotube yarn MET-BFC7 (2.18 mW cm−2). Consequently, we demonstrated that our highly porous metallic cotton fiber-based BFC (MCF-BFC) fabricated by small-molecule linker-induced LbL assembly of the active catalysts can significantly realize the DET rate between the enzymes and the conductive supports. More significantly, the maximum power density of an MCF-BFC can be further increased by simply increasing the bilayers of Au NP layers in the cathode and/or in the anode. Moreover, these controlled electrode–electrode and/or BFC–BFC connections can further increase the overall power density of the device. For example, if two 120-MCF-BFCs were connected in series, the maximum power output measured was ~7.1 mW cm−2, which is an approximately twofold increase in the hybrid BFC performance (Fig. 5e).
We have demonstrated ultrahigh-power hybrid DET-BFCs by using small-molecule-linker-derived metal NPs and enzyme multilayers that not only stimulate electrical communication between the electrochemically active components but also maximize the electrocatalytic activity on highly porous cotton fibers. In addition, we demonstrated that the power performance of the MCF-BFCs could be further enhanced by increasing the electrical conductivity and the electrocatalytic surface area of the MCF through increasing the number of TOA-Au NP/TREN bilayers. Consequently, the areal power density of 3.7 mW cm−2 obtained from the 120-MCF-BFC using a fixed external resistance exhibited the best-reported performance of the BFCs. This result emphasizes the ability of the small-molecule linker-induced LbL assembly to fine-tune the interfacial adsorption onto the highly porous cotton fibers and the structure between the metal NPs and the enzymes, thereby enhancing their electrochemical performance. We believe that our approach can be widely applied to electrode designs for various electrochemical energy storage and conversion devices.
Cotton fibers with a diameter of 200 μm were purchased from Igonji (South Korea), and glucose oxidase (GOx) from Aspergillus niger (180 U mg−1) was purchased from Amano Enzyme Inc. (Japan). Tetraoctylammonium bromide (TOA), gold (III) chloride trihydrate (HAuCl4·3H2O), sodium borohydride (NaBH4), tris-(2-aminoethyl)amine (TREN) (Mw ~146), and polyethylenimine, branched (PEI, Mw ~800 and 25,000) were purchased from Sigma-Aldrich.
Synthesis of tetraoctylammonium bromide-stabilized gold nanoparticles
Tetraoctylammonium bromide-stabilized Au NPs (TOA-Au NPs) with a diameter of 8 nm were synthesized using a two-phase method in toluene43. In brief, HAuCl4·3H2O in water (30 mmol L−1, 30 mL) and TOA in toluene (20 mmol L−1, 80 mL) were mixed with vigorous stirring, and then NaBH4 in water (0.4 mol L−1, 25 mL) was added to the two-phase mixture. After sufficient stirring (approximately 3 h), the aqueous solution was separated from the mixture, and then the remaining toluene solution was repeatedly washed using dilute aqueous H2SO4 (0.1 mol L−1), NaOH (0.1 mol L−1), and deionized water. After several washing steps and the removal of the aqueous solution, TOA-Au NPs dispersed in toluene were obtained.
Fabrication of metallic cotton fiber electrodes
Cotton fibers composed of hydroxy (OH) group-functionalized cellulose fibers were dipped in ethanolic solutions of amine (NH2)-functionalized PEI (Mw ~800; 1 mg mL−1) for 40 min. The resulting PEI-coated fibers, which were prepared through a hydrogen-bonding interaction between the NH2 of PEI and the OH groups of the cotton fibers, were then immersed in a TOA-Au NP solution (10 mg mL−1) for 40 min, and then washed with toluene to remove the weakly adsorbed TOA-Au NPs. In this case, the bulky TOA ligands bound to the surface of the Au NPs were almost completely replaced by NH2 groups of the PEI-coated fibers due to the high affinity between the Au surface and NH2 groups. Next, the formed TOA-Au NP-coated fibers were immersed in a solution of TREN in ethanol (1 mg mL−1) for 40 min. This was repeated, and the fibers were washed in ethanol to remove the excess TREN molecules, resulting in fibers coated with one bilayer (i.e. (TOA-Au NP/TREN)1-cotton fiber). The adsorption mechanism between the TOA-Au NPs and the NH2-functionalized TREN is the same as that between the TOA-Au NPs and PEI. These deposition and washing steps for the preparation of the MCFs were continuously repeated until the desired number of bilayers was obtained.
Fabrication of anode electrodes
The fabricated MCF electrode was immersed in a solution of GOx (5 mg mL−1 in PBS) for 10 min, and then washed with PBS (pH 7.4) to remove weakly adsorbed GOx. During these deposition and washing steps, negatively charged GOx molecules in the pH 7.4 PBS aqueous solution were electrostatically adsorbed onto the positively charged MCF. It should be noted that the neutral NH2 groups of the outermost TREN layer of the MCF prepared in organic phases can be easily protonated to positively charged ammonium (NH3+) groups in pH 7.4 PBS aqueous solution because the pKa (pH with a degree of ionization of 50%) of ammonium groups is approximately 10. After the electrostatic deposition of GOx, a solution of positively charged TREN (1 mg mL−1) was deposited on the anionic GOx-coated MCFs for 10 min, which were then washed with PBS. These processes were repeated until an anode electrode (i.e. (GOx/TREN)m-coated MCF) with the desired number of bilayers (m) was obtained. To prepare the polymer linker-based fiber anode electrode, a solution of cationic PEI (Mw ~25,000; 1 mg mL−1) was used instead of TREN. In this case, all the LbL assembly conditions, except the inclusion of polymer, were exactly the same as those used for the (GOx/TREN)m multilayers.
Characterization and analysis of metallic cotton fiber-based electrodes
The surface and cross-sectional morphologies of the MCF-based BFC electrodes were characterized using FE-SEM (Hitachi S4700, Japan) and AFM (XE-100, Park Systems, South Korea). The adsorption behavior and mechanism of formation of the (TOA-Au NP/TREN)n multilayers were investigated using FTIR spectroscopy in specular mode (Cary 600 spectrometer, Agilent Technologies, USA). The growth and loading amount of the LbL-assembled multilayers were examined using UV−Vis spectroscopy (Lambda 35, Perkin Elmer) on quartz glass, and a QCM (QCM 200, SRS, USA), respectively. In the case of QCM measurement, the mass change (ΔM) per layer was calculated from the QCM frequency change (ΔF) using the Sauerbrey equation65,
where F0, A, ρq, and μq represent the resonant frequency (~5 MHz), the active area (cm2), the density (2.65 g cm−3), and the shear modulus (2.95×1011 g cm−1 s−2) of the QCM electrode, respectively, and this expression can be simplified to ΔF (Hz) = −56.6 × ΔMA (MA indicates mass per unit area).
In a three-electrode system composed of an MCF working electrode, Ag/AgCl reference electrode, and a Pt counter electrode, the top end of the working electrode was firmly connected to a copper wire using commercial silver paste (ELCOAT P-100, CANS, South Korea). After the silver paste was dry, it was additionally insulated with an epoxy adhesive. Cyclic voltammograms of an MCF electrode (diameter 200 µm, length 5.0-mm, active external surface area 3.14 mm2) were measured over the potential range −0.6 to +0.6 V using an electrochemical analyzer (Ivium-n-Stat, Ivium Technologies, Netherlands). All measurements were carried out in an electrochemical cell in batch mode, 50 mL PBS buffer (20 mmol L−1 phosphate and 0.14 mol L−1 NaCl, pH 7.4) at 36.5 °C without stirring. Interelectrode spacing between anode and cathode electrode was ~1 cm, the membrane between two electrodes was not used in this study. In addition, one end of each BFC electrode was fixed by epoxy resin on the glass substrate for avoiding electrical shortage while measuring the power density with the continuous operation. The anodic and cathodic current densities were determined by CV at a constant voltage of +0.6 V for the anode and −0.6 V for the cathode, showing a maximum current density. The normalized current density was respectively obtained by subtracting the current density level in glucose-free PBS at +0.6 V for the anode, and subtracting the current density level in an oxygen-free PBS at −0.6 V for the cathode. The BFC power densities were determined by measuring the current output applying a fixed external resistance (in the range of 1 kΩ~10 MΩ) to control cell potential3,5,66. The experimental set-up for measuring the power density of the complete hybrid MCF-BFC was shown in Supplementary Figure 26a. EIS measurements for the n-MCF electrodes and the m-GOx/n-MCF electrodes were performed over the frequency range 0.2 Hz−100 kHz with a perturbation amplitude of 0.01 V. The impedance spectra (Nyquist plots) of the real (Z′) and imaginary parts (Z″) obtained from the electrochemical BFC cell were processed using the ZView software (ver. 2.8d, Scribner Associates Inc., USA).
The authors declare that the data supporting the findings of this study are available from the corresponding author upon request.
Yahiro, A. T., Lee, S. M. & Kimble, D. O. Bioelectrochemistry: I. Enzyme utilizing biofuel cell studies. Biochim. Biophys. Acta 88, 375–383 (1964).
Barton, S. C., Gallaway, J. & Atanasov, P. Enzymatic biofuel cells for implantable and microscale devices. Chem. Rev. 104, 4867–4886 (2004).
Bandodkar, A. J. et al. Soft, stretchable, high power density electronic skin-based biofuel cells for scavenging energy from human sweat. Energy Environ. Sci. 10, 1581–1589 (2017).
Bandodkar, A. J. Wearable biofuel cells: past, present and future. J. Electrochem. Soc. 164, H3007–H3014 (2017).
Zebda, A. et al. Mediatorless high-power glucose biofuel cells based on compressed carbon nanotube-enzyme electrodes. Nat. Commun. 2, 370 (2011).
Wen, D. & Eychmüller, A. Enzymatic biofuel cells on porous nanostructures. Small 12, 4649–4661 (2016).
Kwon, C. H. et al. High-power biofuel cell textiles from woven biscrolled carbon nanotube yarns. Nat. Commun. 5, 3928 (2014).
Holland, J. T. et al. Engineering of glucose oxidase for direct electron transfer via site-specific gold nanoparticle conjugation. J. Am. Chem. Soc. 133, 19262–19265 (2011).
Guiseppi-Elie, A., Lei, C. & Baughman, R. H. Direct electron transfer of glucose oxidase on carbon nanotubes. Nanotechnology 13, 559–564 (2002).
Coman, V. et al. A direct electron transfer-based glucose/oxygen biofuel cell operating in human serum. Fuel Cells 10, 9–16 (2010).
Cosnier, S., Holzinger, M. & Goff, A. L. Recent advances in carbon nanotube-based enzymatic fuel cells. Front. Bioeng. Biotechnol. 2, 1–6 (2014).
Flexer, V., Brun, N., Courjean, O., Backov, R. & Mano, N. Porous mediator-free enzyme carbonaceous electrodes obtained through integrative chemistry for biofuel cells. Energy Environ. Sci. 4, 2097–2106 (2011).
Campbell, A. S. et al. Membrane/mediator-free rechargeable enzymatic biofuel cell utilizing graphene/single-wall carbon nanotube cogel electrodes. ACS Appl. Mater. Interfaces 7, 4056–4065 (2015).
Magrez, A. et al. Cellular toxicity of carbon-based nanomaterials. Nano Lett. 6, 1121–1125 (2006).
Liu, Y., Zhao, Y., Sun, B. & Chen, C. Understanding the toxicity of carbon nanotubes. Acc. Chem. Res 46, 702–713 (2013).
Yan, Y., Lei, W. Z. & Mao, L. Carbon-nanotube-based glucose/O2 biofuel cells. Adv. Mater. 18, 2639–2643 (2006).
Barton, S. C., Pickard, M., Vazquez-Duhalt, R. & Heller, A. Electroreduction of O2 to water at 0.6 V (SHE) at pH 7 on the ‘wired’ pleurotus ostreatus laccase cathode. Biosens. Bioelectron. 17, 1071–1074 (2002).
Farneth, W. E., Diner, B. A., Gierke, T. D. & D’Amore, M. B. Current densities from electrocatalytic oxygen reduction in laccase/ABTS solutions. J. Electroanal. Chem. 581, 190–196 (2005).
Zilly, A. et al. Influence of NaCl and Na2SO4 on the kinetics and dye decolorization ability of crude laccase from ganoderma lucidum. Int. Biodeter. Biodegr. 65, 340–344 (2011).
Mano, N., Mao, F. & Heller, A. Characteristics of a miniature compartment-less glucose–O2 biofuel cell and its opertion in a living plant. J. Am. Chem. Soc. 125, 6588–6594 (2003).
Hernández, J., Solla-Gullón, J., Herrero, E., Aldaz, A. & Feliu, J. M. Electrochemistry of shape-controlled catalysts: oxygen reduction reaction on cubic gold nanoparticles. J. Phys. Chem. C 111, 14078–14083 (2007).
Liu, M., Zhang, R. & Chen, W. Graphene-supported nanoelectrocatalyzsts for fuel cells: synthesis, properties, and applications. Chem. Rev. 114, 5117–5160 (2014).
Park, M. et al. Amphiphilic layer-by-layer assembly overcoming solvent polarity between aqueous and nonpolar media. J. Am. Chem. Soc. 136, 17213–17223 (2014).
Debe, M. K. Electrocatalyst approaches and challenges for automotive fuel cells. Nature 486, 43–51 (2012).
Taylor, S., Fabbri, E., Levecque, P., Schmidt, T. J. & Conrad, O. The effect of platinum loading and surface morphology on oxygen reduction activity. Electrocatalyst 7, 287–296 (2016).
Decher, G. Fuzzy nanoassemblies: toward layered polymeric multicomposites. Science 277, 1232–1237 (1997).
Caruso, F., Caruso, R. A. & Möhwald, H. Nanoengineering of inorganic and hybrid hollow spheres by colloidal templating. Science 282, 1111–1114 (1998).
Caruso, F. & Schüler, C. Enzyme multilayers on colloid particles: assembly, stability, and enzymatic activity. Langmuir 16, 9595–9603 (2000).
Kim, Y. et al. Stretchable nanoparticle conductors with self-organized conductive pathways. Nature 500, 59–64 (2013).
Shutava, T. G., Kommireddy, D. S. & Lvov, Y. M. Layer-by-Layer enzyme/polyelectrolyte films as a functional protective barrier in oxidizing media. J. Am. Chem. Soc. 128, 9926–9934 (2006).
Ko, Y., Baek, H., Kim, Y., Yoon, M. & Cho, J. Hydrophobic nanoparticle-based nanocomposite films using in situ ligand exchange layer-by-layer assembly and their nonvolatile memory applications. ACS Nano 7, 143–153 (2013).
Scodeller, P. et al. Layer-by-layer self-assmbled osmium polymer-mediated laccase oxygen cathodes for biofuel cells: the role of hydrogen peroxide. J. Am. Chem. Soc. 132, 11132–11140 (2010).
Min, J. et al. Designer dual therapy nanolayered implant coatings eradicate biofilms and accelerate bone tissue repair. ACS Nano 10, 4441–4450 (2016).
Lee, J.-S. et al. Layer-by-layer assembled charge trap memory devices with adjustable electronic properties. Nat. Nanotech. 2, 790–795 (2007).
Lvov, Y., Ariga, K., Ichinose, I. & Kunitake, T. Assembly of multicomponent protein films by means of electrostatic layer-by-layer adsorption. J. Am. Chem. Soc. 117, 6117–6123 (1995).
Deng, C., Chen, J., Nie, Z. & Si, S. A sensitive and stable biosensor based on the direct electrochemistry of glucose oxidase assembled layer-by-layer at the multiwall carbon nanotube-modified electrode. Biosens. Bioelectron. 26, 213–219 (2010).
Hyun, K. H., Han, S. W., Koh, W.-G. & Kwon, Y. Fabrication of biofuel cell containing enzyme catalyst immobilized by layer-by-layer method. J. Power Sources 286, 197–203 (2015).
Ko, Y. et al. Flexible supercapacitor electrodes based on real metal-like cellulose papers. Nat. Commun. 8, 536 (2017).
Walcarius, A., Minteer, S. D., Wang, J., Lin, Y. & Merkoçi, A. Nanomaterials for bio-functionalized electrodes: recent trends. J. Mater. Chem. B 1, 4878–4908 (2013).
Zhao, H. & Ju, H. Multilayer membranes for glucose biosensing via layer-by-layer assembly of multiwall carbon nanotubes and glucose oxidase. Anal. Biochem. 350, 138–144 (2006).
Yehezkeli, O., Tel-Vered, R., Raichlin, S. & Willner, I. Nano-engineered flavin-dependent glucose dehydrogenase/gold nanoparticle-modified electrodes for glucose sensing and biofuel cell applications. ACS Nano 5, 2385–2391 (2011).
Asharani, P. V., Lianwu, Y., Gong, Z. & Valiyaveettil, S. Comparison of the toxicity of silver, gold and platinum nanoparticles in developing zebrafish embryos. Nanotoxicology 5, 43–54 (2011).
Brust, M., Walker, M., Bethell, D., Schiffrin, D. J. & Whyman, R. Synthesis of thiol derivated gold nanoparticles in a two-phase liquid-liquid system. J. Chem. Soc., Chem. Commun. 7, 801–802 (1994).
Zhang, X. et al. Strong carbon-nanotube fibers spun from long carbon-nanotube arrays. Small 3, 244–248 (2007).
Lekawa-Raus, A., Patmore, J., Kurzepa, L., Bulmer, J. & Koziol, K. Electrical properties of carbon nanotube based fibers and their future use in electrical wiring. Adv. Funct. Mater. 24, 3661–3682 (2014).
Zhang, H., Xu, J. & Chen, H. Shape-controlled gold nanoarchitectures: synthesis, superhydrophobicity, and electrocatalytic properties. J. Phys. Chem. C 112, 13886–13892 (2008).
Wang, L. et al. Porous carbon-supported gold nanoparticles for oxygen reduction reaction: effects of nanoparticle size. ACS Appl. Mater. Interfaces 8, 20635–20641 (2016).
Libertino, S., Aiello, V., Scandurra, A., Renis, M. & Sinatra, F. Immobilization of the enzyme glucose oxidase on both bulk and porous SiO2 surfaces. Sensors 8, 5637–5648 (2008).
Pardo-Yissar, V., Katz, E., Lioubashevski, O. & Willner, I. Layered polyelectrolyte films on Au electrodes: characterization of electron-transfer features at the charged polymer interface and application for selective redox reactions. Langmuir 17, 1110–1118 (2001).
Gibson, Q. H., Swoboda, B. E. P. & Massey, V. Kinetics and mechanism of action of glucose oxidase. J. Biol. Chem. 239, 3927–3934 (1964).
Luo, W. J. et al. Self-catalyzed, self-limiting growth of glucose oxidase-mimicking gold nanoparticles. ACS Nano 4, 7451–7458 (2010).
Wang, S. C. et al. Membrane-less and mediator-free enzymatic biofuel cell using carbon nanotube/porous silicon electrodes. Electo. Commun. 11, 34–37 (2009).
Laviron, E. General expression of the linear sweep voltammogram in the case of diffusionless electrochemical systems. J. Electroanal. Chem. 101, 19–28 (1979).
Zhao, M., Gao, Y., Sun, J. & Gao, F. Mediatorless glucose biosensor and direct electron transfer type glucose/air biofuel cell enabled with carbon nanodots. Anal. Chem. 87, 2615–2622 (2015).
Cai, C. & Chen, J. Direct electron transfer of glucose oxidase promoted by carbon nanotubes. Anal. Biochem. 332, 75–83 (2004).
Hong, J. et al. Direct electrochemistry of hemoglobin immobilized on a functionalized multi-walled carbon nanotubes and gold nanoparticles nanocomplex-modified glassy carbon electrode. Sensors 13, 8595–8611 (2013).
Hui, N., Gao, R., Li, X., Sun, W. & Jiao, K. Direct electrochemistry of hemoglobin immobilized in polyvinylalcohol and clay composite film modified carbon ionic liquid electrode. J. Braz. Chem. Soc. 20, 252–258 (2009).
Bao, S. et al. New nanostructured TiO2 for direct electrochemistry and glucose sensor applications. Adv. Funct. Mat. 18, 591–599 (2008).
Halámková, L. et al. Implanted biofuel cell operating in living snail. J. Am. Chem. Soc. 134, 5040–5043 (2012).
Fischer, U. et al. Assessment of subcutaneous glucose concentration: validation of the wick technique as a reference for implanted electrochemical sensors in normal and diabetic dogs. Diabetologia 30, 940–945 (1987).
Wong, L. S. Y. et al. Very low-power CMOS mixed-signal IC for implantable pacemaker applications. IEEE J. Solid-State Circuits 39, 2446–2452 (2004).
Kelly, S. K. & Wyatt, J. L. A power-efficient neural tissue stimulator with energy recovery. IEEE T. Biomed. Circ. S 5, 20–29 (2011).
Saati, S. et al. Mini drug pump for ophthalmic use. Curr. Eye Res. 35, 192–201 (2010).
Yuan, Y., Ahmed, J. & Kim, S. Polyaniline/carbon black composite-supported iron phthalocyanine as an oxygen reduction catalyst for microbial fuel cells. J. Power Sources 196, 1103–1106 (2011).
Buttry, D. A. Advanced in Electroanalytical Chemistry: Applications of the QCM to Electrochemistry (Marcel Dekker Inc., New York, 1991).
du Toit, H. & Di Lorenzo, M. Continuous power generation from glucose with two different miniature flow-through enzymatic biofuel cells. Biosens. Bioelectron. 69, 199–205 (2015).
This work was supported by a National Research Foundation (NRF) grant funded by the Ministry of Science, ICT & Future Planning (MSIP) (2018R1A2A1A05019452; 2016M3A7B4910619) and the Basic Science Research Program through the National Research Foundation of Korea (NRF) funded by the Ministry of Education (NRF-2017R1A6A3A04003192).
The authors declare no competing interests.
Publisher’s note: Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.
About this article
Cite this article
Kwon, C.H., Ko, Y., Shin, D. et al. High-power hybrid biofuel cells using layer-by-layer assembled glucose oxidase-coated metallic cotton fibers. Nat Commun 9, 4479 (2018). https://doi.org/10.1038/s41467-018-06994-5
Applied Sciences (2021)
Advanced Energy and Sustainability Research (2021)
Frontiers in Chemistry (2021)
Interfacial Design and Assembly for Flexible Energy Electrodes with Highly Efficient Energy Harvesting, Conversion, and Storage
Advanced Energy Materials (2021)
Advanced Materials (2021)