Towards an implantable biochip for glucose and lactate monitoring using microdisc electrode arrays (MDEAs)

Rahman, Abdur; Justin, Gusphyl; Guiseppi‐Elie, Anthony

doi:10.1007/s10544-008-9211-6

Cited by 41 publications

(16 citation statements)

References 34 publications

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“…The redox peaks are clearly prominent for the cyclic voltammograms in the Fe(II)/ Fe(III) solution compared to PBS. Plots of peak anodic current normalized to the plan or actual area of each electrode, that is, current density,

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(A/cm 2 ), versus square root of scan rate (Vs −1 ) 1/2 were produced to extract the slope of the linear regression in accordance with the Randles‐Sevcik equation (1) [20, 21]. Because each electrode type was of different plan or geometric area, the slopes then are a direct measure of the relative rank of the effective surface areas.…”

Section: Resultsmentioning

confidence: 99%

Electrode Selection for Electrostimulation and TEER Using ECSARA

2020

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The TransEpithelial/Endothelial Electrical Resistance (TEER) of cells grown in the 24-well electroculture ware of an Electrical Cell Stimulation and Recoding Apparatus (ECSARA) shows well-to-well variation as potentially a function of the electrode material employed in stimulation-interrogation. Six electrode materials were studied; glassy carbon (GCE), graphitic carbon (GrC), titanium (Ti), platinized Type 304 stainless steel (PtSS), platinum (Pt100) and gold (Au). Each unmodified electrode was studied by multiple scan rate cyclic voltammetry (MSRCV) and by electrochemical impedance spectroscopy (EIS) with equivalent circuit analysis (EQCRTA) in PBS and in Fe(II)/Fe(III). MSRCV and Randles-Sevcik analysis of the bare electrodes produced an effective area correction factor γ* that rank-ordered the electrodes GrC = 1.58 > Pt = 1.40 > GCE = 0.94 > Au = 0.66 > PtSS = 0.11 > Ti = 0.01. Tandem EIS-EQCRTA produced R CT (Ω)/γ* of 1.20 × 10 2 and 5.60 × 10 8 for GrC and Ti, respectively and established these two electrode materials as the performance extremes. GrC and Ti were used as electrode materials in the 24-well electroculture ware of ECSARA. The coefficient of variation of the charging capacity extracted from CVs of GrC (22 wells, 10.05 mC) and Ti (22 wells, 1.75 mC) was 51.4 % and 54.6 % respectively, reflective of the difference in surface area. EIS-EQCRTA of GrC and Ti (21 wells) showed both electrodes to faithfully measure the solution resistance, R S , with CV of 54 % and 28 %, respectively, despite the lower charge transfer resistance, R CT , of GrC (R CT = 1.08 × 10 3 Ω, CV = 125 %) compared to Ti (R CT = 1.20 × 10 5 Ω, CV = 30 %). Overall, Ti electrodes were shown to be more appropriate for application in cell stimulation and TEER recording.

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Section: Resultsmentioning

confidence: 99%

Electrode Selection for Electrostimulation and TEER Using ECSARA

2020

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“…Thus, highly stable, accurate intramuscular implantable biosensors for the simultaneous continuous monitoring of tissue lactate and glucose have recently been produced, including a complete electrochemical cell-on-a-chip. Moreover, with the parallel development of the on-chip potentiostat and signal processing, substantial progress has been made towards a wireless implantable glucose/lactate sensing biochip [30]. Elsewhere, implantable bio-micro-electromechanical systems (bio-MEMS) for the in situ monitoring of blood flow have been designed [31].…”

Section: Description and Challenges Of A Customized Biomedical Implanmentioning

confidence: 99%

Design of a Customized Multipurpose Nano-Enabled Implantable System for In-Vivo Theranostics

Juanola-Feliu

Miribel-Català

Avilés

et al. 2014

Sensors

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The first part of this paper reviews the current development and key issues on implantable multi-sensor devices for in vivo theranostics. Afterwards, the authors propose an innovative biomedical multisensory system for in vivo biomarker monitoring that could be suitable for customized theranostics applications. At this point, findings suggest that cross-cutting Key Enabling Technologies (KETs) could improve the overall performance of the system given that the convergence of technologies in nanotechnology, biotechnology, micro&nanoelectronics and advanced materials permit the development of new medical devices of small dimensions, using biocompatible materials, and embedding reliable and targeted biosensors, high speed data communication, and even energy autonomy. Therefore, this article deals with new research and market challenges of implantable sensor devices, from the point of view of the pervasive system, and time-to-market. The remote clinical monitoring approach introduced in this paper could be based on an array of biosensors to extract information from the patient. A key contribution of the authors is that the general architecture introduced in this paper would require minor modifications for the final customized bio-implantable medical device.

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“…Table 1 lists the various monomer and pre-polymer constituents used in the preparation of the poly(HEMA)-based hydrogel and the electrochemically produced P(Py-co-PyBA). The modification and derivatization of gold electrode surfaces for the application of hydrogel and ECH films, including the cleaning procedure, has previously been described [34,36,37] and is illustrated in Schemes 1 and 2.…”

Section: Preparation Of Ech Polymersmentioning

confidence: 99%

Electroconductive Blends of Poly(HEMA-co-PEGMA-co-HMMAco-SPMA) and Poly(Py- co-PyBA): In Vitro Biocompatibility

Justin

Guiseppi‐Elie

2009

Journal of Bioactive and Compatible Polymers

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Electroconductive hydrogels (ECHs) were prepared as blends of ultraviolet cross-linked poly(hydroxyethyl methacrylate) [poly(HEMA)]-based hydrogels and in situ electrochemically synthesized polypyrrole (PPy). ECH blends, with potential for neuronal prosthetic devices, implantable biosensors, and electro-stimulated release devices, were produced on surface functionalized microfabricated and planar gold electrodes. Hydrogels were synthesized from hydroxyethyl methacrylate (HEMA), poly(ethylene glycol) monomethacrylate (PEGMA), N-[tris(hydroxymethyl)methyl]-acrylamide (HMMA), and 3-sulfopropyl methacrylate potassium salt (SPMA) to produce p(HEMA-co-PEGMA-co-HMMA-co-SPMA). The electroconductive polymer component was electropolymerized from pyrrole and 4-(3 0 -pyrrolyl)butyric acid to form P(Py-co-PyBA) within the electrode-supported hydrogel. The dynamic electrochemical properties of Au*|Gel-P(Py-co-PyBA) were investigated using multiple scan rate cyclic voltammetry and electrical/electrochemical impedance spectroscopy (EIS) over the range 0.1-100 kHz and compared to Downloaded from there was a three-fold decrease in the magnitude of the absolute impedance, subsequent to electropolymerization. The in vitro biocompatibility and cytotoxicity of the polymer-modified gold surfaces were investigated using murine pheochromocytoma (PC12) cells and human muscle fibroblasts (RMS13). For Au*|Gel-P(Py-co-PyBA) polymer films prepared with different electropolymerization times of 5, 25, and 50 s, there was an increase in cell proliferation of 49%, 61%, and 6% compared to initial cell seeding. These ECH blends have the desired characteristics of low interfacial impedance and noncytotoxicity that makes them good candidates for in vivo intramuscular and neural studies.

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Towards an implantable biochip for glucose and lactate monitoring using microdisc electrode arrays (MDEAs)

Cited by 41 publications

References 34 publications

Electrode Selection for Electrostimulation and TEER Using ECSARA

Electrode Selection for Electrostimulation and TEER Using ECSARA

Design of a Customized Multipurpose Nano-Enabled Implantable System for In-Vivo Theranostics

Electroconductive Blends of Poly(HEMA-co-PEGMA-co-HMMAco-SPMA) and Poly(Py- co-PyBA): In Vitro Biocompatibility

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