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Paper-Based All-Solid-State Ion-Sensing Platform with a Solid Contact Comprising Colloid-Imprinted Mesoporous Carbon and a Redox Buffer Jinbo Hu, Wenyang Zhao, Philippe Buhlmann, and Andreas Stein ACS Appl. Nano Mater., Just Accepted Manuscript • DOI: 10.1021/acsanm.7b00151 • Publication Date (Web): 21 Nov 2017 Downloaded from http://pubs.acs.org on November 25, 2017

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ACS Applied Nano Materials

Paper-Based All-Solid-State Ion-Sensing Platform with a Solid Contact Comprising Colloid-Imprinted Mesoporous Carbon and a Redox Buffer Jinbo Hu, Wenyang Zhao, Philippe Bühlmann,* and Andreas Stein* Department of Chemistry, University of Minnesota, 207 Pleasant St. SE, Minneapolis, Minnesota 55455, United States *

Corresponding authors, E-mail: [email protected]; [email protected]

Keywords: paper-based sensor, mesoporous carbon, all-solid-state ion-selective electrode, redox buffer, potentiometry, chloride

ACS Paragon Plus Environment

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ABSTRACT We report the design, structure, and performance of a planar paper-based ion-sensing platform that utilizes colloid-imprinted mesoporous (CIM) carbon as a solid contact, with a redox buffer as internal reference. This device contains an all-solid-state ion-selective electrode (ISE) and an all-solid-state reference electrode that are integrated into the paper substrate with a symmetrical cell design. To ensure calibration-free sensor operation, each interfacial potential within the device is well defined by use of a redox buffer added to the sensing and reference membranes that controls the interfacial potentials at the CIM carbon/sensing membrane and CIM carbon/reference membrane interfaces. Two types of redox buffers were evaluated for this purpose, i.e., one based on the tetrakis(pentafluorophenyl)borate salts of cobalt(II/III) tris(4,4’dinonyl-2,2’-bipyridyl), and one consisting of 7,7,8,8-tetracyanoquinodimethane and its corresponding anion radical. The feasibility of the design was demonstrated with aqueous KCl solutions. By design, the device only needs one droplet of sample, and it does not need any supply reagents or sensor pretreatment (i.e., conditioning and calibration) to function.


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INTRODUCTION Due to its abundance, low cost, and suitability for mass manufacturing, paper has recently been extensively explored as a substrate to fabricate disposable analytical platforms with built-in microfluidic channels defined by hydrophobic barriers.1-5 Compared to their conventional counterparts that usually rely on expensive consumables and frequent maintenance, paper-based analytical devices are more affordable and simpler to use, making them very attractive for clinical applications, especially in developing countries with limited resources. Existing paperbased analytical devices rely on different sensing techniques for various analytes. While the colorimetric methods bear the advantage of simple data visualization and interpretation,6 electrochemical detection is insensitive to color interference and is generally more accurate in terms of quantitative analysis.7-9 Ion sensing has long been an interest in analytical chemistry, and is of vital importance in many fields, such as clinical analysis, process management, and environmental analysis.10-14 With the growing demand for point-of-care and in-field testing, increased research efforts have focused on miniaturized ion-sensing systems with small sample volumes, simple operation, reduced cost, and increased compatibility with mass manufacturing techniques, such as printing. Paper and nanostructured transducing solid contact materials are frequently used as key components in these devices.4, 15-18 Depending on the specific sensor design, paper provides different functions for the ion sensors reported in the literature. Paper has long been used as a substrate to mechanically support the other components of the sensor. Disposable strip-type ion sensors with paper as a key component were reported in the 1990s, where a filter paper coated with silver was sandwiched between two insulating layers to mechanically support and electrically connect an ion-selective


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electrode (ISE) membrane.19-20 This sensor design was recently combined with nanostructured or conductive polymer-based solid contact transducing materials to construct high-performance strip-type ion-sensing devices. For example, carbon nanotubes21-23 or graphene24 were deposited onto a paper substrate to serve as an ion-to-electron transducer, and Li+ measurements in whole blood were demonstrated with such a sensor design.22 With an additional hydrophobic layer of sputtered gold and poly(3-octylthiophene) on top of a conductive paper coated with carbon nanotubes, nanomolar detection limits for Cd2+, Ag+, and K+ were achieved.23 Besides providing mechanical support, paper can also be used as a disposable microfluidic sampling tool to replace conventional sample holders (e.g., beakers or tubing), because it transports fluids by capillary forces. It was reported that paper can be sandwiched between an all-solid-state ISE and a reference electrode to transport the sample solutions from other areas to the sensing electrodes.2526

With the addition of a complexing agent into a pretreated microfluidic paper substrate, a

separation system was achieved in which the transport of interfering ions was significantly slowed down by complexation, and thus only the target ion could reach the sensing electrodes.27 For controlled microfluidic sampling, hydrophobic barriers can be deposited onto the paper substrate to define microfluidic channels. For example, a three-dimensional paper-based ion sensor was developed with a conventional reusable poly(vinyl chloride) sensing membrane sandwiched between two disposable paper substrates containing sample and reference zones defined by printed wax. With careful sensor assembly and calibration, various ions could be detected in aqueous sample solutions.28 Although attractive features, such as low detection limits and suitability for biological samples, were demonstrated with the aforementioned state-of-the-art, paper-based ion-sensing devices, those devices all require cumbersome pretreatment protocols including sensor


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conditioning and calibration, which may impede their practical use, especially when they are used by less skilled operators. To address this issue, we previously introduced a conditioningfree and calibration-free paper-based ion-sensing platform that is designed for single-use operation.29 The device is based on a conventional potentiometric cell that is imbedded into the paper substrate, with sample and reference zones defined by a polyurethane hydrophobic barrier. To provide well-defined reference potentials, an inner reference system composed of stencilprinted Ag/AgCl electrodes and KCl reference electrolytes was introduced. Because of the symmetrical cell design and precise control of each interfacial potential, the response of this ionsensing platform can be predicted quantitatively, and the device can be used to detect ion concentrations in undiluted blood serum without prior sensor calibration.29 The use of the Ag/AgCl/KCl inner reference system, however, complicates the measuring protocol by requiring the supply and application of a liquid KCl reference electrolyte. Therefore, it is desirable to eliminate the KCl reference electrolyte, further simplifying the sensor operation. Herein, we report a paper-based all-solid-state ion-sensing device that only requires one droplet of sample and requires neither sensor pretreatment (such as conditioning and calibration) nor externally added reagents (such as reference electrolyte). This device relies on an all-solidstate ISE and an all-solid-state reference electrode that are both based on colloid-imprinted mesoporous (CIM) carbon. CIM carbon is a novel solid contact material that comprises open and interconnected 20–30 nm diameter mesopores with a bicontinuous carbon and pore space.30-31 This unique porous structure provides a large interfacial contacting area between the CIM carbon and the ion-sensing phase with which the carbon is impregnated, thus creating a high double layer interfacial capacitance and leading to high sensor potential stability. Also, CIM carbon exhibits a low amount of redox-active surface functionalities because it is prepared from a high-


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purity mesophase pitch carbon precursor, which is essential to construct electrodes with high electrode-to-electrode reproducibility and excellent resistance to possible oxygen interference.3233

CIM carbon is produced in powder form, which makes CIM carbon compatible with the mass

production methods that are needed to fabricate paper-based sensors on a large scale, such as by inkjet printing. The CIM carbon-based ISE and reference electrodes are integrated into the paper substrate with a symmetrical cell design. Unlike our previously reported device that employed a conventional Ag/AgCl/KCl inner reference system,29 a redox buffer is doped into the ISE and reference membranes to control the interfacial potentials at the CIM carbon/ISE membrane and CIM carbon/reference membrane interfaces, serving as an internal reference system. For this purpose, two types of redox buffers were evaluated, i.e., a cobalt(II/III) tris(4,4’-dinonyl-2,2’bipyridyl) ([Co(II/III)(C9,C9-bipy)3](TPFPB)2/3)34 redox buffer, and the redox couple consisting of 7,7,8,8,-tetracyanoquinodimethane (TCNQ) and the corresponding anion radical.35-36 As a proof of concept, paper-based all-solid-state Cl−-sensing devices were constructed and tested with aqueous solutions. In our previous work we reported the concept of CIM carbon-based reference electrodes on the paper substrate with the [Co(II/III)(C9,C9-bipy)3](TPFPB)2/3 redox buffer.33 Here we extend our work by constructing paper-based devices that comprise both CIM carbon-based sensing and reference electrodes, evaluate a second redox buffer based on TCNQ, discuss the requirements for the redox buffer, report the characterization of the structural features of the device using scanning electron microscopy (SEM), and explore the applications of these devices in biological samples.


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EXPERIMENTAL Materials. Reagents were obtained from the following sources: Fumion FAA-3 ionomer anion exchanger from FuMA-Tech GmbH (Bietigheim-Bissingen, Germany), the ionic liquid 1methyl-3-octylimidazolium bis(trifluoromethylsulfonyl)imide [C8min+][C1C1N−] from IoLiTec (Tuscaloosa, AL, USA), TCNQ, tetraethylammonium tetrafluoroborate, o-nitrophenyl octyl ether (o-NPOE), high molecular weight poly(vinyl chloride) (PVC) from Sigma-Aldrich (St. Louis, MO), Tecoflex SG-80A polyurethane from Thermedic Polymer Products (Woburn, MA), and Autonorm freeze-dried blood serum from SERO (Stasjonsveien, Norway). All chemicals were used as received without further purification. Deionized water was purified to a resistivity of 18.2 MΩ/cm with a Milli-Q PLUS reagent-grade water system (Millipore, Bedford, MA). CIM carbon,30-32 the K+ salt of the TCNQ– radical anion (KTCNQ),37 and the redox couple consisting of [Co(II)(C9,C9-bipy)3](TPFPB)2 and [Co(III)(C9,C9-bipy)3](TPFPB)334 were prepared as previously reported. Precursor Solutions of Sensing and Reference Membranes. Fumion FAA-3 ionomer anion exchanger was used as the sensing membrane and loaded with Cl− counter ions using a previously reported procedure.29 150 mg of Cl−-loaded Fumion FAA-3 ionomer was dissolved in 2 mL of methanol under magnetic stirring. Precursor solutions for reference membranes were prepared by dissolving 60 mg of the ionic liquid [C8min+][C1C1N−], 120 mg of PVC as a polymeric matrix, and 120 mg of o-NPOE as plasticizer in 2 mL of anhydrous tetrahydrofuran. The redox buffers containing 1.4 mmol/kg of [Co(II/III)(C9,C9-bipy)3](TPFPB)2/3 or 3 mmol/kg of TCNQ/KTCNQ were added into both the sensing membrane and reference membrane precursor solutions.


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Fabrication of Paper-Based All-Solid-State Ion-Sensing Platform. Paper-based sample zones and microfluidic channels were defined by patterning polyurethane lines that penetrated the whole thickness of filter paper pieces (Whatman Grade 589/2 white ribbon, GE Healthcare, Chicago, IL). Approximately 2.5 g of polyurethane was dissolved in 40 mL of tetrahydrofuran, and this solution was then applied to both sides of the filter paper using a glass capillary tube, forming polyurethane barriers against hydrophilic samples approximately 2 mm in width. To form sensing and reference membranes of approximately 1 mm width, a 10 µL microcapillary was used to apply the corresponding precursor solutions onto the filter paper. Where necessary, the viscosity of the precursor solutions was adjusted by dilution with additional aliquots of corresponding solvents for better penetration into the filter paper. To ensure full penetration of the membrane components through the entire thickness of the paper, the precursor solutions were applied to both sides of the paper twice each. The CIM carbon-sensing membrane suspension was prepared by ultrasonicating 75 mg of CIM carbon in 1 mL of the sensing membrane precursor solution, including the redox buffer, for 30 min. In a similar way, CIM carbon-reference membrane suspensions were prepared by ultrasonicating for 30 min 60 mg of CIM carbon in 1 mL of the precursor solution containing the reference membrane components, including the redox buffer. The resulting sensing and reference suspensions were then applied onto paper using a capillary to form a homogenous mixture of CIM carbon and the corresponding membranes, with an effort to maximize the contact area between this homogenous mixture and the membrane. Electrochemical Measurements. Electrode potentials were measured with an EMF 16 voltmeter (input impedance 10 TΩ) controlled by EMF Suite 1.03 software (Lawson Labs,


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Malvern, PA). Two copper alligator clips were used to connect the two CIM carbon-based sensing and reference electrodes to the voltmeter. A series of samples containing different concentrations of Cl− and K+ was obtained by sequential dilution of a KCl solution. A series of blood serum samples with various Cl− concentrations was prepared by adding small amounts of a 0.8 M KCl solution into tenfold diluted blood serum. Activity coefficients were calculated according to a two-parameter Debye–Hückel approximation.38 After the samples and reference electrolytes were applied to the corresponding sensing zones, it took approximately 10 s for the solutions to be wicked onto the sensing and reference membranes. Then, the emf response over the following 30 s was measured. Cyclic voltammograms of TCNQ and KTCNQ were obtained at room temperature with a CHI600C potentiostat (CH Instruments, Austin, TX). A three-electrode setup was used, with a gold electrode as the working electrode, a Pt wire as the counter electrode, and a Ag wire in 10 mM AgNO3/acetonitrile as a nonaqueous reference electrode with a CoralPor glass frit for separation from the sample.39 A 0.1 M tetraethylammonium tetrafluoroborate solution with acetonitrile as solvent was used as a supporting electrolyte solution.


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RESULTS AND DISCUSSION Design of the Paper-Based All-Solid-State Ion-Sensing Platform. The ion-sensing platform was fabricated by integrating a CIM carbon-based ISE and a CIM carbon-based reference electrode onto the paper substrate (Figure 1a). The solid contacts comprising CIM carbon and redox buffer were contacted with the corresponding sensing and reference membranes, which were applied separately and embedded into the paper. For a demonstration, the commercial high-capacity ionomer Fumion FAA-3 was used as anion exchanger for Cl− sensing, and the ionic liquid [C8min+][C1C1N−] was doped into the reference membrane to provide a sample-independent reference potential. The hydrophilic Fumion FAA-3 sensing membranes are considered suitable for clinical Cl− sensing because they exhibit much lower interference from hydrophobic anions (e.g., Br− and SCN−) than more hydrophobic ion exchangers.40 Their hydrophilicity also decreases interference from biofouling caused by lipids,40 and because of their high ion-exchange capacity, they have a high resistance to Donnan failure at high ion concentrations.41 The ion-sensing platform utilized a polyurethane-based hydrophobic barrier that defined a sample zone. In this sensor design, paper served both as a microfluidic sampling tool as well as a supportive porous matrix into which the sensing components were embedded.42


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Figure 1. (a) Photograph of an all-solid-state paper-based ion-sensing device with a CIM carbonbased ISE, a CIM carbon-based reference electrode, and a microfluidic sample zone defined by polyurethane. (b) Schematic representation of all relevant interfaces in a paper-based Cl– sensor with a commercial anion exchanger Fumion FAA-3 ionomer film as the sensing membrane and an ionic liquid-doped and plasticized PVC film as reference membrane. Both membranes are doped with a redox buffer containing a redox couple, shown as “Red” and “Ox”. (c) Electrical potential profile across the paper-based all-solid-state ion-sensing platform, with the only sample-dependent interfacial potential being the phase boundary potential at the sensing membrane/sample interface.


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To ensure single-use operation and calibration-free ion sensing, a high reproducibility of the standard electrode potential, E˚, for multiple devices is required.15 This can be achieved by precisely defining each interfacial potential within the device (see Figure 1b). To this end, a redox buffer (i.e., [Co(II/III)(C9,C9-bipy)3](TPFPB)2/3 or TCNQ/KTCNQ) was doped into both the sensing and reference membranes to control the interfacial potentials at the CIM carbon/sensing membrane interface (∆φ1) and the CIM carbon/reference membrane interface (∆φ4). A redox buffer contains both the oxidized and reduced species of a redox couple. Similar to a pH buffer whose pH can be controlled by an acid and its conjugate base, a redox buffer controls the electrical potential to a value that is determined by its standard redox potential and the ratio of the oxidized and reduced species of the redox couple, as predicted by the Nernst equation:43 E = E˚’ +

RT aox ln nF ared

(1)

where E is the electrical potential of the redox buffer, E˚’ is the standard reduction potential of the redox couple, R is the ideal gas constant, F is the Faraday constant, T is the temperature, n is the number of moles of electrons transferred in the redox reaction, and aox and ared are the activities of the oxidized and reduced species of the redox couple, respectively. A few requirements must be fulfilled for an adequate redox buffer. First and foremost, a redox buffer should have a well-defined redox potential. Conductive polymers usually exhibit high redox capacitance, but a continuum of less well-defined redox potentials that can be related to the inhomogeneity in crystallinity, conformation, film morphology, and so on.15 Therefore, compared to molecular redox species that exhibit well-defined redox potentials, conductive polymers are less attractive for redox buffer applications. Secondly, both the oxidized and reduced species of the redox buffer should be chemically and electrochemically stable with


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reversible redox activity. In this regard, the standard reduction potential of the redox couple should be close to 0 V (vs Ag/AgCl) so that the redox couple cannot be easily oxidized or reduced by redox-active interferents that are present in the system. For example, although ferrocene is a well-studied redox molecule with a suitable standard reduction potential of 0.40 V (vs SHE), it cannot be used for redox buffer applications because its oxidized form, the ferrocenium ion, is not stable under certain circumstances. It was reported that Cl– ions can induce the degradation of ferrocenium ions into non-reducible FeCl4– in both organic electrolytes and ferrocene-doped ISE membranes, which can lead to irreversible redox chemistry.44 Furthermore, the redox couple should also exhibit fast electron-transfer rates, thus enabling adequate ion-to-electron transduction when the redox buffer is used as the transducer layer in an all-solid-state ISE. The phase boundary potentials across the other interfaces within the paper-based allsolid-state ion-sensing devices should also be well defined. In this work, the interface between the sensing membrane and the sample (∆φ2) was controlled by partitioning of the primary ion (i.e., Cl−) between the Fumion FAA-3 ionomer film and sample, resulting in an interfacial potential dependent on the Cl− concentration in the sample that can be described quantitatively by the classical phase-boundary-potential model.45 Moreover, the reference membrane was doped with an ionic liquid (i.e., [C8min+][C1C1N−]) that can leach into the sample on a slow but continuous basis, thus providing a constant but sample-independent reference potential at the sample/reference membrane interface (∆φ3).46-47 Therefore, the only sample-dependent interfacial potential within the device was the phase boundary potential at the sensing membrane/sample interface (∆φ2), with all other interfacial potentials being sample-independent and well defined. The measured overall electromotive force (emf) was the electrical potential


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difference between the two CIM carbon-based electrodes, which was the sum of all interfacial potentials within the cell (Figure 1c). By such a design, the correlation between the measured emf and the concentration of Cl− can be established. Structural Features of Paper-Based All-Solid-State Ion-Sensing Platform. The structural features of the ion-sensing platform were characterized by SEM. Figure 2a shows the non-ordered pore structure of the paper substrate made from hydrophilic cellulose fibers, which can be coated and penetrated by the sensing membranes to form well-defined sensing interfaces (Figure 2b and 2f). Unlike in a conventional ISE, in which an inner Ag/AgCl reference half cell is in contact with KCl reference electrolyte solution, the sensing membrane was contacted on the side opposite to the sample with a CIM carbon-based electrode (Figure 2c). The interfacial potential at that interface is stabilized by both the redox reaction of the redox buffer as well as the electrical double layer at the CIM carbon/sensing membrane interface.32,

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A magnified

image of the CIM-carbon based electrode shows a particle size of approximately 10 µm (Figure 2d), and these CIM carbon particles were bound together by the sensing or reference membranes. The highly porous surface of CIM carbon can be observed in the high magnification image in Figure 2e, and the pore size of CIM carbon can be tuned by using Ludox colloidal silica spheres with different particle sizes.30-31 When CIM carbon was mixed with the precursor solution of the sensing membrane under sonication, the sensing components infiltrated the highly interconnected mesopores of CIM carbon to form a bicontinuous, ionically and electronically conducting structure with a large interfacial contacting area and high double layer capacitance.32 Therefore, effective ion-to-electron transduction was achieved. A cross-sectional view of the device is given in Figure 2f. It can be seen that the sensing membrane penetrated the entire


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thickness of the paper substrate, and a good contact was formed between the sensing membrane and the CIM carbon transduction layer.

Figure 2. SEM images of the ion-sensing platform. Top views of (a) the paper substrate, (b) the device showing the interface between the sensing membrane and the sample zone, and (c) the device showing the interface between CIM carbon-based sensing electrode and the sensing membrane. Magnified views of (d) the CIM carbon-based sensing electrode and (e) the uncoated CIM carbon, showing the mesopores. (f) Cross-sectional view of the ion-sensing platform, showing the sensing membrane-infiltrated paper substrate with the CIM carbon-based sensing electrode. Incorporation of a [Co(II/III)(C9,C9-bipy)3](TPFPB)2/3 Redox Buffer. [Co(II)(C9,C9bipy)3](TPFPB)2 and [Co(III)(C9,C9-bipy)3](TPFPB)3 are hydrophobic cobalt complexes with


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bipyridine-based ligands. They are chemically stable under ambient conditions and exhibit a standard reduction potential of approximately –0.35 V (vs Ag/AgCl) with fast electron-transfer rates.34,

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Previously, redox buffers based on [Co(II/III)(C9,C9-bipy)3](TPFPB)2/3 were doped

into ISE and reference membranes to construct all-solid state potentiometric ISEs and reference electrodes with high electrode-to-electrode E˚ reproducibility and minimal oxygen interference due to the high redox buffer capacity.34,

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The combination of [Co(II/III)(C9,C9-

bipy)3](TPFPB)2/3 and CIM carbon lead to highly reproducible all-solid-state ISEs with a standard deviation of E˚ less than 1 mV.32 Therefore, the redox buffer comprising [Co(II/III)(C9,C9-bipy)3](TPFPB)2/3 was also doped into both of the sensing and reference membranes in the current paper-based ion-sensing platform with CIM carbon electrodes. The potentiometric Cl– response of the paper-based all-solid-state ion-sensing platform was evaluated with aqueous KCl sample solutions of different concentrations. For each measurement, 20 µL of the sample was applied to the sample zone of the device, and the potential difference between the two CIM carbon-based electrodes was measured once the sample reached the sensing and reference membranes. Neither prior sensor calibration nor conditioning were needed. Since these devices were designed for single-use operations, a separate device was employed for each data point in the calibration curve. As presented in Figure 3, the paper-based all-solid-state Cl– sensors exhibited a response slope of –60.6 mV/decade and an R2 value of 0.991, which is within error consistent with the theoretically predicted Nernstian response. The observed linear range of the device was from 10-1.1 to 10-3.1 M, with a lower detection limit of 10-3.14 M. This lower detection limit was very close to that of our previously reported paper-based Cl–-sensing device (i.e., 10-3.10 M),29 and appears to be limited by the highcapacity anion exchange film used as the sensing membrane.41 Unlike our previously reported


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paper-based Cl–-sensing device that utilized an Ag/AgCl/KCl inner reference system,29 the current all-solid-state device does not need a reference electrolyte (i.e., KCl solution) to function. An initial evaluation of the new ion sensors with tenfold diluted blood serum samples revealed a good Nernstian response slope of –59.9 mV/decade, but a relatively low linearity with an R2 value of 0.628. We assume that the observed reduced reproducibility is caused by the accelerated loss of the redox buffer into the lipophilic biological samples,34 and we are currently developing new redox buffers that will eliminate this problem.

Figure 3. Potentiometric Cl– calibration curve of the ion-sensing platform with a redox buffer consisting of [Co(II/III)(C9,C9-bipy)3](TPFPB)2/3. The response was obtained with KCl solutions. Each data point corresponds to one individual device.

Conventional-Size All-Solid-State ISEs with TCNQ/KTCNQ as a Redox Buffer. Besides [Co(II/III)(C9,C9-bipy)3](TPFPB)2/3, a redox couple consisting of TCNQ and its ionradical salt KTCNQ was also evaluated as a redox buffer. TCNQ has long been of interest in molecular electronics due to its ability to accept electrons to form simple and stable charge-


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transfer complexes and ion-radical salts.37,

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TCNQ ion-radical salts were used in

potentiometric ion sensors as early as in the 1970s, where they were employed as solid-state ionselective membranes based on the selective distribution of the primary ion (e.g., Ag+) between the sample solution and TCNQ ion-radical salts (e.g., AgTCNQ).54 Recent publications by Paczosa-Bator et al. report outstanding electrochemical performance of all-solid-state ISEs based on TCNQ, NaTCNQ, or a mixture of the two.35-36 They reported that a high electrode E˚ reproducibility was achieved with a standard deviation of E˚ as low as 1.4 mV when TCNQ was used as the ion-to-electron transducer between a glassy carbon electrode and a K+-ISE membrane.35 In follow-up work,36 TCNQ and NaTCNQ were mixed with various carbon nanomaterials (i.e., graphene, carbon nanotubes, ordered mesoporous carbon CMK-3, and carbon black) with a 1:1:1 weight ratio to serve as the solid contact. The resulting all-solid-state ISEs all exhibited good electrode E˚ reproducibility with a standard deviation of E˚ less than 4.0 mV. The reported potential stability is remarkable as well, with a drift less than 10 µV/h over a measuring period of 72 h.36 Notably, in these two papers, a high E˚ reproducibility was observed after the electrodes had been conditioned in aqueous solutions for 24 h. This is very different from the all-solid-state K+-ISEs based on the [Co(II/III)(C9,C9-bipy)3](TPFPB)2/3 redox buffer, which exhibited significantly decreased E˚ reproducibility upon electrode conditioning due to the loss of redox buffer into the aqueous solution in contact with the redoxbuffer-containing membrane (i.e., the standard deviation of E˚ increased from 0.7 mV after 1 h of conditioning to 16.3 mV after 24 h of electrode conditioning).34 The reported data suggest that TCNQ and its ion-radical salt may not suffer as much from the leaching problem as the [Co(II/III)(C9,C9-bipy)3](TPFPB)2/3 redox buffer does, and appear to be an effective redox buffer pair. Therefore, the use of TCNQ/TCNQ− as redox buffer was also used tested in this work.


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TCNQ is known to exhibit two reversible one-electron redox processes, in which TCNQ is first reduced to TCNQ˙− and then further reduced to TCNQ2−.55-56 Cyclic voltammograms for TCNQ and KTCNQ are shown in Figure S1. Since the observed standard potential of the TCNQ˚/˙− redox process is close to 0 V, both the oxidized and reduced species within the redox couple are expected to be quite stable under ambient conditions. The voltammograms show that the TCNQ/KTCNQ couple is a good candidate for the preparation a redox buffer, not only because of its chemical and electrochemical stability but also because of the fast and reversible electron transfer. To further evaluate the effectiveness of E˚ control of the TCNQ/KTCNQ redox buffer in potentiometric ion sensing, 3 mmol/kg of TCNQ and KTCNQ in a 1:1 molar ratio were doped into sensing membranes to construct conventional-size (non-planar) ISEs with a CIM carbonbased solid contact. These bulk electrodes comprised CIM carbon films separating an underlying gold electrode from a Fumion FAA-3 ionomer anion exchanger sensing membrane (i.e., the same electrode configuration as reported previously32-33; see Figure S2). The sensing membranes were doped with TCNQ/KTCNQ. To study the effect of electrode conditioning on the E˚ reproducibility, Cl– calibrations were performed without electrode conditioning (i.e., no prior contact with aqueous solutions) and after conditioning the electrodes in a 1 mM KCl solution for 24 h. When the electrodes were tested with aqueous KCl solutions without conditioning (Figure 4a), a linear response was obtained with a close to Nernstian slope of –53.9 ± 1.2 mV/decade and a fairly reproducible E˚ of –47.0 ± 4.3 mV (n = 5). This E˚ reproducibility is in good agreement with the literature that reports use of TCNQ/NaTCNQ with other nanostructured carbon materials to construct all-solid-state ISEs. Specifically, standard deviations of E˚ of 2.4


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mV for graphene, 3.7 mV for carbon nanotubes, 3.2 mV for carbon black, and 3.2 mV for the ordered mesoporous carbon CMK-3 were reported.36 However, after conditioning the electrodes for 24 h, larger electrode-to-electrode variations were observed in this work, with the standard deviation of E˚ increasing to 14.0 mV (Figure 4b). This observation is very similar to that of allsolid-state K+-ISEs based on the [Co(II/III)(C9,C9-bipy)3](TPFPB)2/3 redox buffer, whose standard deviation of E˚ increased from 0.7 to 16.3 mV after conditioning the electrodes in an aqueous solution for additional 23 h.34 The diminished electrode-to-electrode E˚ reducibility was also accompanied with an E˚ drift of 32.1 mV (i.e., from –47.0 mV to –14.9 mV), indicating that the ratio of TCNQ/KTCNQ present in the sensing membrane may have changed. The all-solid-state ISEs with the TCNQ/KTCNQ redox buffer were also tested with tenfold diluted blood serum samples, where similar results were observed. Compared to aqueous samples, tenfold diluted blood serum samples are more lipophilic, which may accelerate leaching of the redox buffer into the sample. Figure 5 presents the Cl– calibration curves of CIM carbonbased electrodes with the TCNQ/KTCNQ redox buffer as obtained in tenfold diluted blood serum samples. It can be seen that without any electrode conditioning (Figure 5a), the electrodes exhibited a sub-Nernstian slope of –39.4 ± 3.4 mV/decade and a good electrode E˚ reducibility of –33.8 ± 4.4 mV. After 24 h of electrode conditioning (Figure 5b), the response slope improved to –53.8 ± 1.0 mV/decade, but the electrode E˚ reproducibility decreased to 10.4 ± 19.0 mV (n = 6) with a drift of 44.2 mV. It is likely that the reduced electrode-to-electrode E˚ reproducibility was caused by leaching of TCNQ/KTCNQ into the sample. Although these results suggest that TCNQ/KTCNQ is not suitable for application as a redox buffer in potentiometric ion sensors for long-term measurements, it may be still used for single-use devices, where the device is typically only contacted with the sample over a very short period of time. Since the total measuring time


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of the paper-based all-solid-state ion-sensing devices is 30 s, a redox buffer containing TCNQ/KTCNQ can be used for such disposable paper-based devices.

Figure 4. Potentiometric Cl– calibration curves of CIM carbon-based all-solid-state bulk electrodes with a TCNQ/KTCNQ redox buffer doped into the sensing membrane (n = 5). (a) Response to KCl solutions without electrode conditioning. (b) Response to KCl solutions after conditioning the electrodes in a 1 mM KCl solution for 24 h.


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Figure 5. Potentiometric Cl– calibration curves of CIM carbon-based all-solid-state bulk electrodes with a TCNQ/KTCNQ redox buffer doped into the sensing membrane (n = 6). (a) Response to tenfold diluted blood serum samples without electrode conditioning. (b) Response to tenfold diluted blood serum samples after conditioning the electrodes in a 1 mM KCl solution for 24 h.

Paper-Based All-Solid-State Ion-Sensing Platform with a TCNQ/KTCNQ Redox Buffer. The TCNQ/KTCNQ couple was used to dope the sensing and reference membranes (3 mmol/kg) of the paper-based all-solid-state ion-sensing platform. The potentiometric Cl–


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calibration curve of the resulting devices is shown in Figure 6, in which a close to Nernstian response was acquired with a slope of –63.6 mV/decade and an R2 value of 0.984. When the devices were tested with tenfold diluted blood serum samples, the Nernstian response appears to be preserved, but with a lower R2 value of 0.856. Combined with the results from [Co(II/III)(C9,C9-bipy)3](TPFPB)2/3 redox buffer, these results demonstrate the feasibility of the current sensor design but also show that a more robust redox buffer system that will not leach out is needed for measurements of blood samples. For meaningful clinical measurements, a very high electrode reproducibility is required. According to the U.S. Code of Federal Regulations,57 in clinical laboratories the acceptable measuring error for Cl– is ±5%, which corresponds to a variation in emf value of approximately 1.1 mV. Covalent attachment of the redox buffer to CIM carbon or the sensing membrane may be promising solutions to achieve such high device-todevice reproducibility.

Figure 6. Potentiometric Cl– calibration curve of all-solid-state paper-based ion-sensing platform with a TCNQ/KTCNQ redox buffer doped into both the sensing and reference membranes. The response was measured with KCl solutions (solid circle) and tenfold diluted blood serum samples (open circle). Each data point is based on one device.


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CONCLUSIONS This paper reports the design, structure, and performance of a disposable paper-based allsolid-state ion-sensing platform that is based on a CIM carbon solid contact and a redox buffer. The transduction mechanism of the sensor is based on a design in which each phase boundary potential is well defined, and the structural features of the device are fully characterized. Unlike previously reported paper-based ion sensors, this all-solid-state device does not require any sensor pretreatment or reference electrolyte to function. Also, this planar device is compatible with mass production techniques such as printing. Proof-of-concept paper-based all-solid-state Cl– sensors were constructed, and the feasibility of the sensor design was demonstrated with aqueous KCl solutions with two types of redox buffers, namely [Co(II/III)(C9,C9bipy)3](TPFPB)2/3 and TCNQ/KTCNQ. For measurements in biological samples, a more robust redox buffer system is still required as it appears that the leaching of the redox buffer limits the long-term stability of the sensors. Covalent attachment of the redox buffer to the sensing membrane or CIM carbon appears to be a promising solution.

SUPPORTING INFORMATION The Supporting Information is available free of charge on the ACS Publications website at DOI:XXXXXXXX Cyclic voltammograms for TCNQ and KTCNQ (Figure S1) and schematic diagram of a CIM carbon-based, all-solid-state ISE used to evaluate the effectiveness of the TCNQ/KTCNQ redox buffer (Figure S2).


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ACKNOWLEDGEMENTS The University of Minnesota Initiative for Renewable Energy and the Environment supported this work. J.H. thanks the Krogh family for a Lester C. and Joan M. Krogh Fellowship, and the Graduate School of the University of Minnesota for a Doctoral Dissertation Fellowship. We thank Carl Schu from Medtronic PLC (industrial fellow of the Industrial Partnership for Research in Interfacial and Materials Engineering, IPRIME, program) for valuable discussions.


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(57) Laboratory Requirements, Code of Federal Regulations, Section 493.931, Title 42, 2003.


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Paper-Based All-Solid-State Ion-Sensing Platform ... - ACS Publications

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