Numerical Modeling and Investigation of Amperometric Biosensors with Perforated Membranes
"> Figure 1
<p>Schematic view of the biosensor with cylindrical holes.</p> "> Figure 2
<p>The geometries of the biosensor unit cell: (<b>a</b>) cylindrical, (<b>b</b>) upward circular cone, (<b>c</b>) downward circular cone, (<b>d</b>) upward paraboloid, (<b>e</b>) downward paraboloid, (<b>f</b>) upward concave paraboloid, and (<b>g</b>) downward concave paraboloid. Figures are not to scale.</p> "> Figure 3
<p>Comparison between the results of the present study with [<a href="#B10-sensors-20-02910" class="html-bibr">10</a>]: (<b>a</b>) variation in the dynamic current of the biosensor with the time and thickness of the enzyme membrane (<span class="html-italic">d</span>) for <span class="html-italic">V<sub>max</sub></span> = 10<sup>−7</sup> mol/cm<sup>3</sup>s; (<b>b</b>) dependency of the maximal current of the biosensor on the maximal enzymatic rate (<span class="html-italic">V<sub>max</sub></span>) and the thickness of the enzyme membrane.</p> "> Figure 4
<p>Comparison between the results of the present study with [<a href="#B13-sensors-20-02910" class="html-bibr">13</a>]: (<b>a</b>) concentration profiles of glucose and H<sub>2</sub>O<sub>2</sub> in a multi-layer sensor system consisting of GO<sub>x</sub>/PPD (20 nm) and HAs/Fe<sup>3+</sup> (100 nm); (<b>b</b>) dependency of the maximal current of the biosensor on the glucose concentration with 20 nm of GO<sub>x</sub>/PPD and 100 nm of HAs/Fe<sup>3+</sup>.</p> "> Figure 5
<p>Comparison between the results of the present study and Baronas [<a href="#B20-sensors-20-02910" class="html-bibr">20</a>] in cylindrical geometry for different values of the enzyme filling level (<span class="html-italic">γ</span>) and the perforation level (<span class="html-italic">α</span>): <span class="html-italic">V<sub>max</sub></span> = 100 μM. (1) <span class="html-italic">a</span><sub>1</sub> = 1 μm, <span class="html-italic">S</span><sub>0</sub> = 1 μM; (2) <span class="html-italic">a</span><sub>1</sub> = 0.8 μm, <span class="html-italic">S</span><sub>0</sub> = 100 μM; (3) <span class="html-italic">a</span><sub>1</sub> = 0.4 μm, <span class="html-italic">S</span><sub>0</sub> = 100 μM.</p> "> Figure 6
<p>Comparison between the results of the present study with the experimental data of [<a href="#B31-sensors-20-02910" class="html-bibr">31</a>]; variation in the dynamic current of the biosensor with time and for two substrate concentrations: <span class="html-italic">S</span><sub>0</sub> = 0.49 and 0.99 mol/m<sup>3</sup>.</p> "> Figure 7
<p>Dependency of the output current on the perforation level (<math display="inline"><semantics> <mrow> <mi>γ</mi> <mo>=</mo> <mn>0.5</mn> </mrow> </semantics></math>): (<b>a</b>) <math display="inline"><semantics> <mrow> <mi>α</mi> <mo>=</mo> <mn>0.2</mn> </mrow> </semantics></math>, (<b>b</b>) <math display="inline"><semantics> <mrow> <mi>α</mi> <mo>=</mo> <mn>0.8</mn> </mrow> </semantics></math>. The enzyme filling level (<math display="inline"><semantics> <mrow> <mi>α</mi> <mo>=</mo> <mn>0.5</mn> </mrow> </semantics></math>); (<b>c</b>) <math display="inline"><semantics> <mrow> <mi>γ</mi> <mo>=</mo> <mn>0.05</mn> </mrow> </semantics></math>; (<b>d</b>) <math display="inline"><semantics> <mrow> <mi>γ</mi> <mo>=</mo> <mn>0.95</mn> </mrow> </semantics></math>.</p> "> Figure 8
<p>Dependency of the steady-state biosensor current on the perforation level: (<b>a</b>) <math display="inline"><semantics> <mrow> <mi>γ</mi> <mo>=</mo> <mn>0.05</mn> </mrow> </semantics></math>, (<b>b</b>) <math display="inline"><semantics> <mrow> <mi>γ</mi> <mo>=</mo> <mn>0.95</mn> </mrow> </semantics></math>. The enzyme filling level: (<b>c</b>) <math display="inline"><semantics> <mrow> <mi>α</mi> <mo>=</mo> <mn>0.35</mn> </mrow> </semantics></math>, (<b>d</b>) <math display="inline"><semantics> <mrow> <mi>α</mi> <mo>=</mo> <mn>0.8</mn> </mrow> </semantics></math>.</p> "> Scheme 1
<p>Different regions of an amperometric biosensor.</p> ">
Abstract
:1. Introduction
2. Structure of the Biosensor
3. Formulation of the Problem
4. Dimensionless Mathematical Model
5. Numerical Approach
6. Validation of Computations
7. Results and Discussion
8. Conclusions
Author Contributions
Funding
Conflicts of Interest
References
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α | γ | Cylindrical | Upward Circular Cone | Downward Circular Cone | Upward Paraboloid | Downward Parabolic | Upward Concave Paraboloid | Downward Concave Paraboloid |
---|---|---|---|---|---|---|---|---|
0.5 | 0.05 | 0.87 | 1.04 | 0.91 | 0.99 | 0.86 | 1.08 | 0.98 |
0.5 | 0.95 | 1.02 | 1.33 | 1.20 | 1.23 | 1.06 | 1.42 | 1.22 |
0.5 | 0.5 | 0.92 | 1.11 | 1.18 | 1.05 | 0.97 | 1.19 | 1.14 |
0.2 | 0.5 | 0.86 | 1.10 | 0.96 | 1.01 | 0.91 | 1.16 | 1.05 |
0.8 | 0.5 | 1.07 | 1.21 | 1.19 | 1.23 | 1.12 | 1.33 | 1.37 |
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Hashem Zadeh, S.M.; Heidarshenas, M.; Ghalambaz, M.; Noghrehabadi, A.; Saffari Pour, M. Numerical Modeling and Investigation of Amperometric Biosensors with Perforated Membranes. Sensors 2020, 20, 2910. https://doi.org/10.3390/s20102910
Hashem Zadeh SM, Heidarshenas M, Ghalambaz M, Noghrehabadi A, Saffari Pour M. Numerical Modeling and Investigation of Amperometric Biosensors with Perforated Membranes. Sensors. 2020; 20(10):2910. https://doi.org/10.3390/s20102910
Chicago/Turabian StyleHashem Zadeh, Seyed Mohsen, Mohammadhosein Heidarshenas, Mohammad Ghalambaz, Aminreza Noghrehabadi, and Mohsen Saffari Pour. 2020. "Numerical Modeling and Investigation of Amperometric Biosensors with Perforated Membranes" Sensors 20, no. 10: 2910. https://doi.org/10.3390/s20102910