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3 pages, 878 KiB  
Abstract
A Portable Gold-Nanoparticle-Enhanced Surface Plasmon Resonance Sensor for Highly Sensitive β-Bungarotoxin Quantification in Snake Poisoning Diagnosis
by Samuel Husin Surya Mandala, Mochamad Januar, Chien-Chun Liu, Jau-Song Yu and Kou-Chen Liu
Proceedings 2024, 97(1), 229; https://doi.org/10.3390/proceedings2024097229 - 25 Sep 2024
Abstract
This study introduces a portable gold-nanoparticle-enhanced surface plasmon resonance (SPR) biosensor for the swift and highly sensitive detection of β-bungarotoxin in krait venom. Demonstrating a 103-fold increase in sensitivity over traditional SPR sensors, this compact tool underscores the potential of portable [...] Read more.
This study introduces a portable gold-nanoparticle-enhanced surface plasmon resonance (SPR) biosensor for the swift and highly sensitive detection of β-bungarotoxin in krait venom. Demonstrating a 103-fold increase in sensitivity over traditional SPR sensors, this compact tool underscores the potential of portable SPR biosensors for efficient point-of-care venom diagnostics. Full article
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Figure 1

Figure 1
<p>(<b>a</b>) Schematic illustration of the operation procedure of the handheld SPR sensor for directly detecting β-btx in serum samples. (<b>b</b>) Comparison of different SPR reflection spectra either with or without AuNPs. (<b>c</b>) A comparison of two different SPR responses either with or without AuNPs at a fixed β-btx concentration of 500 fg mL<sup>−1</sup>. (<b>d</b>) SPR response as a function of β-btx concentration either with or without AuNPs. (<b>e</b>) SPR responses for reading and scoring the krait bite severity level.</p>
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12 pages, 3557 KiB  
Article
A Point-of-Care Testing Device Utilizing Graphene-Enhanced Fiber Optic SPR Sensor for Real-Time Detection of Infectious Pathogens
by Shiyu Jiang, Siyu Qian, Shunning Zhu, Jinxin Lu, Yunxin Hu, Cheng Zhang, Yikai Geng, Xuefeng Chen, Ying Guo, Zhaoliang Chen, Jie Pu, Zhendong Guo and Shengchun Liu
Biosensors 2023, 13(12), 1029; https://doi.org/10.3390/bios13121029 - 14 Dec 2023
Cited by 3 | Viewed by 1799
Abstract
Timely detection of highly infectious pathogens is essential for preventing and controlling public health risks. However, most traditional testing instruments require multiple tedious steps and ultimately testing in hospitals and third-party laboratories. The sample transfer process significantly prolongs the time to obtain test [...] Read more.
Timely detection of highly infectious pathogens is essential for preventing and controlling public health risks. However, most traditional testing instruments require multiple tedious steps and ultimately testing in hospitals and third-party laboratories. The sample transfer process significantly prolongs the time to obtain test results. To tackle this aspect, a portable fiber optic surface plasmon resonance (FO-SPR) device was developed for the real-time detection of infectious pathogens. The portable device innovatively integrated a compact FO-SPR sensing component, a signal acquisition and processing system, and an embedded power supply unit. A gold-plated fiber is used as the FO-SPR sensing probe. Compared with traditional SPR sensing systems, the device is smaller size, lighter weight, and higher convenience. To enhance the detection capacity of pathogens, a monolayer graphene was coated on the sensing region of the FO-SPR sensing probe. Severe acute respiratory syndrome coronavirus 2 (SARS-CoV-2) was used to evaluate the performance of the portable device. The device can accurately detect the SARS-CoV-2 spike S1 protein in phosphate-buffered saline (PBS) and artificial saliva within just 20 min, and the device successfully detected cultured SARS-CoV-2 virus. Furthermore, the FO-SPR probe has long-term stability, remaining stable for up to 8 days. It could distinguish between the SARS-CoV-2 spike protein and the MERS-CoV spike protein. Hence, this FO-SPR device provides reliable, rapid, and portable access to test results. It provides a promising point-of-care testing (POCT) tool for on-site screening of infectious pathogens. Full article
(This article belongs to the Section Biosensors and Healthcare)
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Figure 1
<p>Scheme of the bio-functionalized FO-SPR sensing probe.</p>
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<p>Schematic depiction of the POCT FO-SPR device. (<b>A</b>) Portable FO-SPR optical sensing scheme (<b>I</b>) FO-SPR sensing component. (<b>II</b>) Signal acquisition and processing system. (<b>III</b>) Embedded power supply unit. (<b>IV</b>) WIFI remote control module. (<b>B</b>) FO-SPR sensing probe.</p>
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<p>SEM, Raman spectra and XPS of pristine and modified FO-SPR sensing probe. (<b>A</b>) SEM image of modified FO-SPR sensing probe. (<b>B</b>) Raman spectra of pristine graphene (black) and PBASE-modified graphene (red). (<b>C</b>) XPS of pristine graphene (black) and PBASE-modified graphene (blue). (<b>D</b>) XPS N 1 s peaks of pristine graphene (black) and PBASE-modified graphene (blue). (<b>E</b>) Deconvolution of PBASE-modified graphene C 1 s peaks.</p>
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<p>Testing SARS-CoV-2 spike S1 protein by portable FO-SPR device. (<b>A</b>) Schematic diagram of the antibody functionalized sensing probe. (<b>B</b>) SPR spectra of antibody functionalized sensing probes exposed to different concentrations of spike protein (10–60 nM). The arrow indicates the direction of the SPR signal offset. (<b>C</b>) Real-time wavelength shift curves with specific antibodies (red) and without specific antibodies (blue). (<b>D</b>) Linear fit of the maximum wavelength shift with spike protein concentrations. The error bars were determined by the standard deviation of three tests.</p>
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<p>Selectivity testing (<b>A</b>) SPR spectra and (<b>B</b>) real-time response curves for SARS-CoV-2 spike S1 protein and MERS-CoV spike protein. (<b>C</b>) Repeatability test (the error bars were determined by the standard deviation of five tests). (<b>D</b>) Long-term stability tests for FO-SPR sensing probes stored in 4 °C PBS for 0 and 8 days. (<b>E</b>) Real-time response curves for testing of SARS-CoV-2 spike protein in artificial saliva. (<b>F</b>) Linear fit of the maximum wavelength shift with spike protein concentration. The error bars were determined by the standard deviation of three tests.</p>
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<p>Testing of SARS-CoV-2 inactivated virus in PBS. (<b>A</b>) Schematic diagram of the antibody functionalized FO-SPR sensing probe for detecting SARS-CoV-2 virus. (<b>B</b>) SPR spectra for different SARS-CoV-2 virus concentrations (5 × 10<sup>3</sup> TCID<sub>50</sub>/mL to 6 × 10<sup>4</sup> TCID<sub>50</sub>/mL). The arrow indicates the direction of the SPR signal offset. (<b>C</b>) Real-time wavelength shift curves with specific antibodies (red) and without specific antibodies (black). (<b>D</b>) Linear fit of the wavelength shifts to different SARS-CoV-2 concentrations. Error bars were determined from the standard deviation of three tests.</p>
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18 pages, 2693 KiB  
Review
Nanobiosensing Based on Electro-Optically Modulated Technology
by Shuang Li, Ziyue Qin, Jie Fu and Qiya Gao
Nanomaterials 2023, 13(17), 2400; https://doi.org/10.3390/nano13172400 - 23 Aug 2023
Cited by 1 | Viewed by 1286
Abstract
At the nanoscale, metals exhibit special electrochemical and optical properties, which play an important role in nanobiosensing. In particular, surface plasmon resonance (SPR) based on precious metal nanoparticles, as a kind of tag-free biosensor technology, has brought high sensitivity, high reliability, and convenient [...] Read more.
At the nanoscale, metals exhibit special electrochemical and optical properties, which play an important role in nanobiosensing. In particular, surface plasmon resonance (SPR) based on precious metal nanoparticles, as a kind of tag-free biosensor technology, has brought high sensitivity, high reliability, and convenient operation to sensor detection. By applying an electrochemical excitation signal to the nanoplasma device, modulating its surface electron density, and realizing electrochemical coupling SPR, it can effectively complete the joint transmission of electrical and optical signals, increase the resonance shift of the spectrum, and further improve the sensitivity of the designed biosensor. In addition, smartphones are playing an increasingly important role in portable mobile sensor detection systems. These systems typically connect sensing devices to smartphones to perceive different types of information, from optical signals to electrochemical signals, providing ideas for the portability and low-cost design of these sensing systems. Among them, electrochemiluminescence (ECL), as a special electrochemically coupled optical technology, has good application prospects in mobile sensing detection due to its strong anti-interference ability, which is not affected by background light. In this review, the SPR is introduced using nanoparticles, and its response process is analyzed theoretically. Then, the mechanism and sensing application of electrochemistry coupled with SPR and ECL are emphatically introduced. Finally, it extends to the relevant research on electrochemically coupled optical sensing on mobile detection platforms. Full article
(This article belongs to the Special Issue Advanced Nanomaterials and Nanotechnologies for Micro/Nano-Sensors)
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Figure 1
<p>Wavelength Potential Extinction Spectra: (<b>a</b>) The relationship between the wavelength, potential, and extinction spectra of plasma nanoparticles. (<b>b</b>) The cross-section at <span class="html-italic">E</span><sub>1</sub> and <span class="html-italic">E</span><sub>2</sub>. (<b>c</b>) The cross-section at <span class="html-italic">λ</span><sub>3</sub>. (<b>d</b>) The relationship between the corresponding wavelength, potential, and extinction spectrum when the refractive index is <span class="html-italic">n<sub>A</sub></span> and <span class="html-italic">n<sub>B</sub></span>. (<b>e</b>) The cross-section at <span class="html-italic">E<sub>c</sub></span>. (<b>f</b>) The cross-section at <span class="html-italic">λ<sub>D</sub></span>. [<a href="#B31-nanomaterials-13-02400" class="html-bibr">31</a>].</p>
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<p>Electrochemically coupled SPR sensing applications: (<b>a</b>) Electrochemical CV scanning for BSA detection. (<b>b</b>) Transmission spectra of nanoCA for BSA detection [<a href="#B34-nanomaterials-13-02400" class="html-bibr">34</a>]. (<b>c</b>) Dopamine detection: CV current unraveled in the time domain. (<b>d</b>) Dopamine detection: spectral responses of the nanosensor as a function of scanning time [<a href="#B35-nanomaterials-13-02400" class="html-bibr">35</a>].</p>
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<p>Electrochemically coupled SPR sensing applications: (<b>a</b>) Heavy metal detection [<a href="#B36-nanomaterials-13-02400" class="html-bibr">36</a>]. (<b>b</b>) Thrombin detection [<a href="#B37-nanomaterials-13-02400" class="html-bibr">37</a>]. (<b>c</b>) Sialic acid detection [<a href="#B38-nanomaterials-13-02400" class="html-bibr">38</a>].</p>
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<p>ECL excitation. (<b>a</b>) Rechargeable battery: lithium battery [<a href="#B76-nanomaterials-13-02400" class="html-bibr">76</a>]. (<b>b</b>) Rechargeable battery: nickel–metal hydride battery [<a href="#B77-nanomaterials-13-02400" class="html-bibr">77</a>]. (<b>c</b>) Supercapacitors [<a href="#B78-nanomaterials-13-02400" class="html-bibr">78</a>]. (<b>d</b>,<b>e</b>) Smartphone audio port [<a href="#B79-nanomaterials-13-02400" class="html-bibr">79</a>]. (<b>f</b>) Smartphone USB-OTG [<a href="#B80-nanomaterials-13-02400" class="html-bibr">80</a>].</p>
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<p>(<b>a</b>) Smartphone USB-OTG: nanocomposites and system [<a href="#B81-nanomaterials-13-02400" class="html-bibr">81</a>]. (<b>b</b>) Smartphone-based electrochemiluminescence system with reaction chamber and electrodes [<a href="#B82-nanomaterials-13-02400" class="html-bibr">82</a>]. (<b>c</b>) Thermal power supply [<a href="#B83-nanomaterials-13-02400" class="html-bibr">83</a>]. (<b>d</b>) Self-powered 3D paper chip [<a href="#B84-nanomaterials-13-02400" class="html-bibr">84</a>].</p>
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<p>Luminescent detector: (<b>a</b>) Red-green-blue ECL using a digital camera as the detector [<a href="#B86-nanomaterials-13-02400" class="html-bibr">86</a>]. (<b>b</b>) Digital camera visualization with a radio luminescence array [<a href="#B87-nanomaterials-13-02400" class="html-bibr">87</a>]. (<b>c</b>) Paper-based microfluidics electrodes and smartphone-based ECL detection platforms [<a href="#B88-nanomaterials-13-02400" class="html-bibr">88</a>]. (<b>d</b>) Handheld ECL detection platform [<a href="#B89-nanomaterials-13-02400" class="html-bibr">89</a>].</p>
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20 pages, 3210 KiB  
Review
Point-of-Care Diagnostic Devices for Detection of Escherichia coli O157:H7 Using Microfluidic Systems: A Focused Review
by Naseem Abbas, Sehyeon Song, Mi-Sook Chang and Myung-Suk Chun
Biosensors 2023, 13(7), 741; https://doi.org/10.3390/bios13070741 - 17 Jul 2023
Cited by 8 | Viewed by 2991
Abstract
Bacterial infections represent a serious and global threat in modern medicine; thus, it is very important to rapidly detect pathogenic bacteria, such as Escherichia coli (E. coli) O157:H7. Once treatments are delayed after the commencement of symptoms, the patient’s health quickly [...] Read more.
Bacterial infections represent a serious and global threat in modern medicine; thus, it is very important to rapidly detect pathogenic bacteria, such as Escherichia coli (E. coli) O157:H7. Once treatments are delayed after the commencement of symptoms, the patient’s health quickly deteriorates. Hence, real-time detection and monitoring of infectious agents are highly critical in early diagnosis for correct treatment and safeguarding public health. To detect these pathogenic bacteria, many approaches have been applied by the biosensors community, for example, widely-used polymerase chain reaction (PCR), enzyme-linked immunosorbent assay (ELISA), culture-based method, and adenosine triphosphate (ATP) bioluminescence. However, these approaches have drawbacks, such as time-consumption, expensive equipment, and being labor-intensive, making it critical to develop ultra-sensitive and highly selective detection. The microfluidic platform based on surface plasmon resonance (SPR), electrochemical sensing, and rolling circle amplification (RCA) offers proper alternatives capable of supplementing the technological gap for pathogen detection. Note that the microfluidic biochip allows to develop rapid, sensitive, portable, and point-of-care (POC) diagnostic tools. This review focuses on recent studies regarding accurate and rapid detection of E. coli O157:H7, with an emphasis on POC methods and devices that complement microfluidic systems. We also examine the efficient whole-body detection by employing antimicrobial peptides (AMPs), which has attracted growing attention in many applications. Full article
(This article belongs to the Special Issue Biosensors Based on Microfluidic Devices)
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<p>The principle of SPR as a label-free biosensing technology and SPR-based microfluidic platform for <span class="html-italic">E. coli</span> detection as a POC. (<b>a</b>) The incident light travels along the dielectric interface and excites plasmon at this interface. (<b>b</b>) Accurate binding of a biomolecule (antibody) on the surface of a gold film results in a shift in SPR resonance angle with before antibody binding θ<sub>1</sub> (blue) and after binding θ<sub>2</sub> (red). The occurrence of binding is denoted as the reflectivity angle (ΔR) with the measured resonance angle fixed. Reprinted with permission from [<a href="#B26-biosensors-13-00741" class="html-bibr">26</a>]. (<b>c</b>) The disposable microfluidic chips, which are surface activated, are placed on the top of the device. (<b>d</b>) The electronic configuration of the device is depicted from bottom to top. A light-emitting diode (LED) illuminates a cylindrical lens, which focuses the light onto a rectangular prism. The reflected light is captured by a CMOS sensor, and the image is transmitted to a portable computer via control circuitry. (<b>e</b>) The schematic shows a microfluidic integrated SPR platform. Reprinted with permission from [<a href="#B24-biosensors-13-00741" class="html-bibr">24</a>].</p>
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<p>The schematic of (<b>a</b>) the impedance-based microfluidic biosensor for accurate and rapid detection of <span class="html-italic">E. coli</span> O157:H7, where the top cover is made of PDMS flexible material. The device features one inlet port through which the antigen passes and one outlet port through which the antigen exits after the reaction. (<b>b</b>) The focusing region is magnified to enhance clarity. (<b>c</b>) The microfluidic arrays consist of a series of sensing regions with gold electrodes embedded under epoxy-based negative photoresist (SU8) microchannels. Reprinted with permission from [<a href="#B37-biosensors-13-00741" class="html-bibr">37</a>]. (<b>d</b>) The principle of the microfluidic impedance biosensor enables continuous-flow pathogen detection. Reprinted with permission from [<a href="#B38-biosensors-13-00741" class="html-bibr">38</a>].</p>
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<p>The principle of a microfluidic biosensor based on dual RCA for the whole cell detection of <span class="html-italic">E. coli</span> O157:H7. (<b>a</b>) An actual image of the microfluidic detection platform shows a single inlet and outlet ports. (<b>b</b>) A schematic illustrates a sandwich detection system where the surface of a microfluidic channel is modified with polyamidoamine (PAMAM) dendrimers. In situ capturing RCA (cRCA) is performed to generate repeating aptamers that capture the target cells. Subsequently, detection signals are amplified using signaling RCA (sRCA). The immobilized dendrimers on the PDMS surface provide several handles, allowing for more copies and higher density of dispersed cRCA on the capturing surface. Reprinted with permission from [<a href="#B53-biosensors-13-00741" class="html-bibr">53</a>].</p>
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<p>The principle of the binding reaction in the case of AMP-immobilized microfluidic biosensor for <span class="html-italic">E. coli</span> O157:H7 detection. (Step I) The AMPs with C-terminal are immobilized on a gold QCM electrode surface. (Step II) The surface is blocked with mercaptohexanol (MCH) to inhibit unnecessary sites for enhancement of the signal−to−noise ratio. (Step III) Implementation and detection of <span class="html-italic">E. coli</span> occur. Reprinted with permission from [<a href="#B70-biosensors-13-00741" class="html-bibr">70</a>].</p>
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<p>Illustration of a microfluidic biosensor based on AMP-embedded glass microbeads for <span class="html-italic">E. coli</span> detection, featuring both detection and regeneration modes. The weir structure of the microfluidic system plays a crucial role in facilitating the proper binding of <span class="html-italic">E. coli</span> on the glass microbeads. Reprinted with permission from [<a href="#B68-biosensors-13-00741" class="html-bibr">68</a>].</p>
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<p>Schematics of AMP magainin I, with a C-terminal cysteine residue labeled onto the surface of glass microbeads, demonstrating the specific binding of both PI-stained nonpathogenic bacteria (<span class="html-italic">E. coli</span> DH5α) and DAPI-stained pathogenic bacteria (<span class="html-italic">E. coli</span> O157:H7) to the AMP-labeled beads. Reprinted with permission from [<a href="#B68-biosensors-13-00741" class="html-bibr">68</a>].</p>
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11 pages, 1661 KiB  
Article
Portable Surface Plasmon Resonance Detector for COVID-19 Infection
by Maciej Trzaskowski, Anna Mazurkiewicz-Pisarek, Jakub Waldemar Trzciński, Marcin Drozd, Rafał Podgórski, Anna Zabost and Ewa Augustynowicz-Kopeć
Sensors 2023, 23(8), 3946; https://doi.org/10.3390/s23083946 - 13 Apr 2023
Cited by 5 | Viewed by 1963
Abstract
Methods based on nucleic acid detection are currently the most commonly used technique in COVID-19 diagnostics. Although generally considered adequate, these methods are characterised by quite a long time-to-result and the necessity to prepare the material taken from the examined person—RNA isolation. For [...] Read more.
Methods based on nucleic acid detection are currently the most commonly used technique in COVID-19 diagnostics. Although generally considered adequate, these methods are characterised by quite a long time-to-result and the necessity to prepare the material taken from the examined person—RNA isolation. For this reason, new detection methods are being sought, especially those characterised by the high speed of the analysis process from the moment of sampling to the result. Currently, serological methods of detecting antibodies against the virus in the patient’s blood plasma have attracted much attention. Although they are less precise in determining the current infection, such methods shorten the analysis time to several minutes, making it possible to consider them a promising method for screening tests in people with suspected infection. The described study investigated the feasibility of a surface plasmon resonance (SPR)-based detection system for on-site COVID-19 diagnostics. A simple-to-use portable device was proposed for the fast detection of anti-SARS-CoV-2 antibodies in human plasma. SARS-CoV-2-positive and -negative patient blood plasma samples were investigated and compared with the ELISA test. The receptor-binding domain (RBD) of spike protein from SARS-CoV-2 was selected as a binding molecule for the study. Then, the process of antibody detection using this peptide was examined under laboratory conditions on a commercially available SPR device. The portable device was prepared and tested on plasma samples from humans. The results were compared with those obtained in the same patients using the reference diagnostic method. The detection system is effective in the detection of anti-SARS-CoV-2 with the detection limit of 40 ng/mL. It was shown that it is a portable device that can correctly examine human plasma samples within a 10 min timeframe. Full article
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<p>Graphical representation of the used test procedure for plasma sample measurement with SPR chip. Created with BioRender.com.</p>
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<p>SPR signal against antibody concentration in the buffer.</p>
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<p>The SPR signal obtained during the experiment including 7 samples on a single chip. Raw data from measurement and control channels.</p>
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<p>Results of the detection of seven plasma samples. Results compared with the reference according to the ELISA test.</p>
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26 pages, 1774 KiB  
Review
Progress in Plasmonic Sensors as Monitoring Tools for Aquaculture Quality Control
by Gabriela Elizabeth Quintanilla-Villanueva, Jesús Maldonado, Donato Luna-Moreno, José Manuel Rodríguez-Delgado, Juan Francisco Villarreal-Chiu and Melissa Marlene Rodríguez-Delgado
Biosensors 2023, 13(1), 90; https://doi.org/10.3390/bios13010090 - 5 Jan 2023
Cited by 12 | Viewed by 3565
Abstract
Aquaculture is an expanding economic sector that nourishes the world’s growing population due to its nutritional significance over the years as a source of high-quality proteins. However, it has faced severe challenges due to significant cases of environmental pollution, pathogen outbreaks, and the [...] Read more.
Aquaculture is an expanding economic sector that nourishes the world’s growing population due to its nutritional significance over the years as a source of high-quality proteins. However, it has faced severe challenges due to significant cases of environmental pollution, pathogen outbreaks, and the lack of traceability that guarantees the quality assurance of its products. Such context has prompted many researchers to work on the development of novel, affordable, and reliable technologies, many based on nanophotonic sensing methodologies. These emerging technologies, such as surface plasmon resonance (SPR), localised SPR (LSPR), and fibre-optic SPR (FO-SPR) systems, overcome many of the drawbacks of conventional analytical tools in terms of portability, reagent and solvent use, and the simplicity of sample pre-treatments, which would benefit a more sustainable and profitable aquaculture. To highlight the current progress made in these technologies that would allow them to be transferred for implementation in the field, along with the lag with respect to the most cutting-edge plasmonic sensing, this review provides a variety of information on recent advances in these emerging methodologies that can be used to comprehensively monitor the various operations involving the different commercial stages of farmed aquaculture. For example, to detect environmental hazards, track fish health through biochemical indicators, and monitor disease and biosecurity of fish meat products. Furthermore, it highlights the critical issues associated with these technologies, how to integrate them into farming facilities, and the challenges and prospects of developing plasmonic-based sensors for aquaculture. Full article
(This article belongs to the Special Issue Women in Biosensors)
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<p>Major areas of interest in aquaculture monitoring.</p>
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<p>Schematic representation of prism-based surface plasmon resonance, fibre-optic SPR, and localised SPR.</p>
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<p>(<b>A</b>) Schematic representation of types of recognition elements and (<b>B</b>) Assay formats.</p>
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<p>Roadmap of the implementation of plasmonic techniques and different recognition elements for their use in aquaculture.</p>
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15 pages, 5445 KiB  
Article
Development of a Single-Chain Variable Fragment of CR3022 for a Plasmonic-Based Biosensor Targeting the SARS-CoV-2 Spike Protein
by Taufik Ramdani Tohari, Isa Anshori, Umi Baroroh, Antonius Eko Nugroho, Gilang Gumilar, Shinta Kusumawardani, Sari Syahruni, Brian Yuliarto, Wyanda Arnafia, Irvan Faizal, Yeni Wahyuni Hartati, Toto Subroto and Muhammad Yusuf
Biosensors 2022, 12(12), 1133; https://doi.org/10.3390/bios12121133 - 6 Dec 2022
Cited by 4 | Viewed by 2318
Abstract
Two years after SARS-CoV-2 caused the first case of COVID-19, we are now in the “new normal” period, where people’s activity has bounced back, followed by the easing of travel policy restrictions. The lesson learned is that the wide availability of accurate and [...] Read more.
Two years after SARS-CoV-2 caused the first case of COVID-19, we are now in the “new normal” period, where people’s activity has bounced back, followed by the easing of travel policy restrictions. The lesson learned is that the wide availability of accurate and rapid testing procedures is crucial to overcome possible outbreaks in the future. Therefore, many laboratories worldwide have been racing to develop a new point-of-care diagnostic test. To aid continuous innovation, we developed a plasmonic-based biosensor designed explicitly for portable Surface Plasmon Resonance (SPR). In this study, we designed a single chain variable fragment (scFv) from the CR3022 antibody with a particular linker that inserted a cysteine residue at the second position. It caused the linker to have a strong affinity to the gold surface through thiol-coupling and possibly become a ready-to-use bioreceptor toward a portable SPR gold chip without purification steps. The theoretical affinity of this scFv on spike protein was −64.7 kcal/mol, computed using the Molecular Mechanics Generalized Born Surface Area (MM/GBSA) method from the 100 ns molecular dynamics trajectory. Furthermore, the scFv was produced in Escherichia coli BL21 (DE3) as a soluble protein. The binding activity toward Spike Receptor Binding Domain (RBD) SARS-CoV-2 was confirmed with a spot-test, and the experimental binding free energy of −10.82 kcal/mol was determined using portable SPR spectroscopy. We hope this study will be useful in designing specific and low-cost bioreceptors, particularly early in an outbreak when the information on antibody capture is still limited. Full article
(This article belongs to the Section Optical and Photonic Biosensors)
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<p>Molecular design of scFv.</p>
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<p>Structure model of scFv in blue and RBD of SARS-CoV-2 in red (<b>A</b>); Model assessed by Ramachandran plot (<b>B</b>) and z-score analysis (<b>C</b>).</p>
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<p>RMSD of protein backbone (<b>A</b>) Residual RMSF profile throughout 100 ns of simulation (<b>B</b>).</p>
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<p>SASA analysis of cysteine residue in the linker.</p>
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<p>Molecular interaction between scFv in blue and RBD in red (<b>A</b>) Hydrogen bond is depicted with a green dashed line; the salt bridge is depicted with an orange dashed line, and hydrophobic interactions are depicted with a pink dashed line (<b>B</b>).</p>
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<p>(<b>A</b>). SDS-PAGE electropherogram (1) the scFvs (2) periplasmic protein of <span class="html-italic">E. coli</span> BL21 (DE3) without recombinant plasmid IPTG induced (3) and IPTG uninduced (<b>B</b>). Spot test Analysis (1) 0.5 mg/mL scFv (2) periplasmic protein of <span class="html-italic">E. coli</span> BL21 (DE3) without recombinant plasmid (3) 0.5 mg/mL BSA in the third lane (<b>B</b>).</p>
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<p>(<b>A</b>) Preparation of the SPR sensor chip: immobilization of scFv, blocking with BSA, and response signal scFv-RBD interactions, (<b>B</b>) magnification image of SPR sensorgram scFv-RBD binding interactions, (<b>C</b>) binding interaction between scFv and various concentrations of RBD, (<b>D</b>) Non-linear fitting of experimental data by Hills and Dubinin-Radushkevich adsorption isotherm model, and (<b>E</b>) SPR dynamic response of IgY to 100 ng/mL SARS-CoV-2 RBD.</p>
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<p>(<b>A</b>) SPR response dynamics and (<b>B</b>) bar chart of scFv response to AI, IB, and their mixture with Spike RBD of SARS-CoV-2 (SC2).</p>
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<p>SPR response dynamics of the developed chip sensor to nasopharyngeal samples.</p>
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18 pages, 3872 KiB  
Article
Synthesis of Molecularly Imprinted Polymer Nanoparticles for SARS-CoV-2 Virus Detection Using Surface Plasmon Resonance
by Aabha Bajaj, Jakob Trimpert, Ibrahim Abdulhalim and Zeynep Altintas
Chemosensors 2022, 10(11), 459; https://doi.org/10.3390/chemosensors10110459 - 5 Nov 2022
Cited by 17 | Viewed by 3308
Abstract
COVID-19 caused by a SARS-CoV-2 infection was first reported from Wuhan, China, and later recognized as a pandemic on March 11, 2020, by the World Health Organization (WHO). Gold standard nucleic acid and molecular-based testing have largely satisfied the requirements of early diagnosis [...] Read more.
COVID-19 caused by a SARS-CoV-2 infection was first reported from Wuhan, China, and later recognized as a pandemic on March 11, 2020, by the World Health Organization (WHO). Gold standard nucleic acid and molecular-based testing have largely satisfied the requirements of early diagnosis and management of this infectious disease; however, these techniques are expensive and not readily available for point-of-care (POC) applications. The COVID-19 pandemic of the 21st century has emphasized that medicine is in dire need of advanced, rapid, and cheap diagnostic tools. Herein, we report on molecularly imprinted polymer nanoparticles (MIP-NPs/nanoMIPs) as plastic antibodies for the specific detection of SARS-CoV-2 by employing a surface plasmon resonance (SPR) sensor. High-affinity MIP-NPs directed against SARS-CoV-2 were manufactured using a solid-phase imprinting method. The MIP-NPs were then characterized using dynamic light scattering (DLS) and atomic force microscopy (AFM) prior to their incorporation into a label-free portable SPR device. Detection of SARS-CoV-2 was studied within a range of 104–106 PFU mL−1. The MIP-NPs demonstrated good binding affinity (KD = 0.12 pM) and selectivity toward SARS-CoV-2. The AFM, cyclic voltammetry, and square-wave voltammetry studies revealed the successful stepwise preparation of the sensor. A cross-reactivity test confirmed the specificity of the sensor. For the first time, this study demonstrates the potential of molecular imprinting technology in conjunction with miniaturized SPR devices for the detection of SARS-CoV-2 particles with high-affinity and specificity. Such sensors could help monitor and manage the risks related to virus contamination and infections also beyond the current pandemic. Full article
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<p>Detailed schematic of solid-phase synthesis of nanoMIPs for SARS-CoV-2 virus.</p>
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<p>Major steps involved in the immobilization of nanoMIPs and detection of the virus.</p>
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<p>(<b>a</b>) Hydrodynamic size distribution of nanoMIPs specific for SARS-CoV-2 (<span class="html-italic">n</span> = 3). (<b>b</b>) Quality of DLS measurement (correlation fit). (<b>c</b>). Average zeta potential measurement centered at −24.79 mV (<span class="html-italic">n</span> = 3).</p>
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<p>(<b>a</b>) Real-time nanoMIP immobilization onto the SPR chip surface. (<b>b</b>) Real-time SPR sensorgram of cumulative SARS-CoV-2 detection assay. (<b>c</b>) Overall results of concentration-dependent virus binding assays using the nanoMIP-SPR sensor (<span class="html-italic">n</span> = 3). The error bars are determined by the standard deviation of several measurements taken on separate sensor chips at each particular concentration. (<b>d</b>) Virus detection on three individual sensor chips.</p>
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<p>(<b>a</b>) Real-time nanoMIP immobilization onto the SPR chip surface. (<b>b</b>) Real-time SPR sensorgram of cumulative SARS-CoV-2 detection assay. (<b>c</b>) Overall results of concentration-dependent virus binding assays using the nanoMIP-SPR sensor (<span class="html-italic">n</span> = 3). The error bars are determined by the standard deviation of several measurements taken on separate sensor chips at each particular concentration. (<b>d</b>) Virus detection on three individual sensor chips.</p>
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<p>AFM images of (<b>a</b>) bare silicon wafer, (<b>b</b>) drop-casted SARS-CoV-2 nanoMIPs at 1 µm × 1 µm and (<b>c</b>) 3 µm × 3 µm scales.</p>
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<p>(<b>a</b>) Surface topography (height images) and (<b>b</b>) phase analysis of different steps involved in nanoMIPs immobilization and SARS-CoV-2 binding.</p>
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<p>Average root-mean-square roughness at each step of immobilization and virus binding (<span class="html-italic">n</span> = 10).</p>
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<p>(<b>a</b>) CV and (<b>b</b>) square-wave voltammograms recorded for immobilization of SARS-CoV-2 nanoMIPs on MUDA-coated gold wires. All measurements were taken with 10 mM K<sub>3</sub>(Fe(CN)<sub>6</sub>) in 0.1 M KCl at room temperature. Each voltammogram represents the average results of three measurements.</p>
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<p>(<b>a</b>) Binding isotherms fitted to the relative response of experimental results from specific binding. (<b>b</b>) Fitting parameters obtained for Langmuir, Freundlich and Langmuir–Freundlich binding models.</p>
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<p>(<b>a</b>) Sensogram of SARS-CoV-2 and HAdV binding at two different concentrations, (<b>b</b>) Overall comparison of relative SPR signal for target non-specific virus species, (<b>c</b>) Cartoon of coronavirus and (<b>d</b>) adenovirus.</p>
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12 pages, 980 KiB  
Article
Cadmium Ions’ Trace-Level Detection Using a Portable Fiber Optic—Surface Plasmon Resonance Sensor
by Bianca-Georgiana Şolomonea, Luiza-Izabela Jinga, Vlad-Andrei Antohe, Gabriel Socol and Iulia Antohe
Biosensors 2022, 12(8), 573; https://doi.org/10.3390/bios12080573 - 27 Jul 2022
Cited by 16 | Viewed by 2916
Abstract
Environmental pollution with cadmium (Cd) is a major concern worldwide, with prolonged exposure to this toxic heavy metal causing serious health problems, such as kidney damage, cancer, or cardiovascular diseases, only to mention a few. Herein, a gold-coated reflection-type fiber optic–-surface plasmon resonance [...] Read more.
Environmental pollution with cadmium (Cd) is a major concern worldwide, with prolonged exposure to this toxic heavy metal causing serious health problems, such as kidney damage, cancer, or cardiovascular diseases, only to mention a few. Herein, a gold-coated reflection-type fiber optic–-surface plasmon resonance (Au-coated FO-SPR) sensor is manufactured and functionalized with (i) bovine serum albumin (BSA), (ii) chitosan, and (iii) polyaniline (PANI), respectively, for the sensitive detection of cadmium ions (Cd2+) in water. Then, the three sensor functionalization strategies are evaluated and compared one at a time. Out of these strategies, the BSA-functionalized FO-SPR sensor is found to be highly sensitive, exhibiting a limit of detection (LOD) for Cd2+ detection at nM level. Moreover, the presence of Cd2+ on the FO-SPR sensor surface was confirmed by the X-ray photoelectron spectroscopy (XPS) technique and also quantified consecutively for all the above-mentioned functionalization strategies. Hence, the BSA-functionalized FO-SPR sensor is sensitive, provides a rapid detection time, and is cheap and portable, with potential applicability for monitoring trace-level amounts of Cd within environmental or potable water. Full article
(This article belongs to the Special Issue New Progress in Optical Fiber-Based Biosensors)
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<p>Schematic diagram of the portable FO-SPR sensing system.</p>
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<p>FO-SPR sensor specificity measurements. (<b>A</b>) Control test, showing that, in the absence of any Cd<math display="inline"><semantics> <msup> <mrow/> <mrow> <mn>2</mn> <mo>+</mo> </mrow> </msup> </semantics></math>-sensitive layer on the Au-coated sensor, only an SPR wavelength shift of ∼2 nm is recorded for the 1 <math display="inline"><semantics> <mi mathvariant="sans-serif">μ</mi> </semantics></math>M Cd<math display="inline"><semantics> <msup> <mrow/> <mrow> <mn>2</mn> <mo>+</mo> </mrow> </msup> </semantics></math> solution. (<b>B</b>) Evaluation of the BSA/Au-coated FO-SPR sensor’s selectivity for detection of 1 <math display="inline"><semantics> <mi mathvariant="sans-serif">μ</mi> </semantics></math>M Cd<math display="inline"><semantics> <msup> <mrow/> <mrow> <mn>2</mn> <mo>+</mo> </mrow> </msup> </semantics></math>, Zn<math display="inline"><semantics> <msup> <mrow/> <mrow> <mn>2</mn> <mo>+</mo> </mrow> </msup> </semantics></math>, and Co<math display="inline"><semantics> <msup> <mrow/> <mrow> <mn>2</mn> <mo>+</mo> </mrow> </msup> </semantics></math> metal ions, respectively, in aqueous solutions. The error bars represent standard deviation (<span class="html-italic">n</span> = 3).</p>
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<p>SPR spectra for varying concentrations from 0 to 1 <math display="inline"><semantics> <mi mathvariant="sans-serif">μ</mi> </semantics></math>M of Cd<math display="inline"><semantics> <msup> <mrow/> <mrow> <mn>2</mn> <mo>+</mo> </mrow> </msup> </semantics></math> using (<b>A</b>) BSA, (<b>C</b>) chitosan, and (<b>E</b>) PANI/Au-coated FO-SPR sensors. (<b>B</b>,<b>D</b>,<b>F</b>) Corresponding calibration curves of the FO-SPR sensors. The error bars represent standard deviation (<span class="html-italic">n</span> = 3).</p>
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<p>XPS spectra of the FO-SPR sensors’ surfaces. Wide scan of (<b>A</b>) BSA/Au, (<b>C</b>) chitosan/Au, and (<b>E</b>) PANI/Au-coated FO-SPR sensors after 1 <math display="inline"><semantics> <mi mathvariant="sans-serif">μ</mi> </semantics></math>M Cd<math display="inline"><semantics> <msup> <mrow/> <mrow> <mn>2</mn> <mo>+</mo> </mrow> </msup> </semantics></math> detection, respectively; (<b>B</b>,<b>D</b>,<b>F</b>) Corresponding core-level spectra of the Cd<math display="inline"><semantics> <msup> <mrow/> <mrow> <mn>2</mn> <mo>+</mo> </mrow> </msup> </semantics></math> immobilized on the functionalized Au-coated FO-SPR sensors.</p>
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11 pages, 2485 KiB  
Article
A Fiber-Based SPR Aptasensor for the In Vitro Detection of Inflammation Biomarkers
by Yu Hua, Ridong Wang and Dachao Li
Micromachines 2022, 13(7), 1036; https://doi.org/10.3390/mi13071036 - 29 Jun 2022
Cited by 10 | Viewed by 2853
Abstract
It is widely accepted that the abnormal concentrations of different inflammation biomarkers can be used for the early diagnosis of cardiovascular disease (CVD). Currently, many reported strategies, which require extra report tags or bulky detection equipment, are not portable enough for onsite inflammation [...] Read more.
It is widely accepted that the abnormal concentrations of different inflammation biomarkers can be used for the early diagnosis of cardiovascular disease (CVD). Currently, many reported strategies, which require extra report tags or bulky detection equipment, are not portable enough for onsite inflammation biomarker detection. In this work, a fiber-based surface plasmon resonance (SPR) biosensor decorated with DNA aptamers, which were specific to two typical inflammation biomarkers, C-reactive protein (CRP) and cardiac troponin I (cTn-I), was developed. By optimizing the surface concentration of the DNA aptamer, the proposed sensor could achieve a limit of detection (LOD) of 1.7 nM (0.204 μg/mL) and 2.5 nM (57.5 ng/mL) to CRP and cTn-I, respectively. Additionally, this biosensor could also be used to detect other biomarkers by immobilizing corresponding specific DNA aptamers. Integrated with a miniaturized spectral analysis device, the proposed sensor could be applied for constructing a portable instrument to provide the point of care testing (POCT) for CVD patients. Full article
(This article belongs to the Special Issue Physics in Micro/Nano Devices: From Fundamental to Application)
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<p>(<b>A</b>) The manufactory process of the biosensor: (i) fiber preparation; (ii) cladding layer exfoliation; (iii) chromium deposition; (iv) gold deposition; (v) sensor packaging; (vi) flow chamber packaging (<b>B</b>) The surface modification of the biosensor. (<b>C</b>) The scheme of the whole detection system.</p>
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<p>(<b>A</b>) The XPS evaluation of the sensing area of the biosensor. (<b>B</b>) The SEM evaluation of the sensing area of the biosensor. (<b>C</b>,<b>D</b>) The infiltration characteristics of the glass sheet before and after the oxygen plasma treatment. (<b>E</b>,<b>F</b>) The surface morphology of the glass sheet with and without oxygen plasma treatment.</p>
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<p>(<b>A</b>) The measurement principle of SPR biosensors. (<b>B</b>) The normalized spectrum of the sensor under solutions with different RIs. (<b>C</b>) The relationship between the SPR wavelength and the refractive index of the solutions.</p>
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<p>The sensor’s response to the CRP (<b>A</b>) and cTn-I (<b>B</b>) under different concentration aptamer modification. The responses of the sensors were modified with different concentration aptamers under the 111 nM CRP (<b>C</b>) and cTn-I (<b>D</b>). The response and the detection limit of the biosensor to CRP (<b>E</b>) and cTn-I (<b>F</b>).</p>
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<p>The selectivity of the biosensor: (<b>A</b>) the sensor modified with the CRP aptamer; (<b>B</b>) the sensor modified with the cTn-I aptamer.</p>
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<p>The repeatability of the biosensor: (<b>A</b>) the sensor modified with the CRP aptamer; (<b>B</b>) the sensor modified with the cTn-I aptamer.</p>
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8 pages, 2528 KiB  
Communication
Numerical Study of Graphene/Au/SiC Waveguide-Based Surface Plasmon Resonance Sensor
by Wei Du, Lucas Miller and Feng Zhao
Biosensors 2021, 11(11), 455; https://doi.org/10.3390/bios11110455 - 15 Nov 2021
Cited by 8 | Viewed by 2481
Abstract
A new waveguide-based surface plasmon resonance (SPR) sensor was proposed and investigated by numerical simulation. The sensor consists of a graphene cover layer, a gold (Au) thin film, and a silicon carbide (SiC) waveguide layer on a silicon dioxide/silicon (SiO2/Si) substrate. [...] Read more.
A new waveguide-based surface plasmon resonance (SPR) sensor was proposed and investigated by numerical simulation. The sensor consists of a graphene cover layer, a gold (Au) thin film, and a silicon carbide (SiC) waveguide layer on a silicon dioxide/silicon (SiO2/Si) substrate. The large bandgap energy of SiC allows the sensor to operate in the visible and near-infrared wavelength ranges, which effectively reduces the light absorption in water to improve the sensitivity. The sensor was characterized by comparing the shift of the resonance wavelength peak with change of the refractive index (RI), which mimics the change of analyte concentration in the sensing medium. The study showed that in the RI range of 1.33~1.36, the sensitivity was improved when the graphene layers were increased. With 10 graphene layers, a sensitivity of 2810 nm/RIU (refractive index unit) was achieved, corresponding to a 39.1% improvement in sensitivity compared to the Au/SiC sensor without graphene. These results demonstrate that the graphene/Au/SiC waveguide SPR sensor has a promising use in portable biosensors for chemical and biological sensing applications, such as detection of water contaminations (RI = 1.33~1.34), hepatitis B virus (HBV), and glucose (RI = 1.34~1.35), and plasma and white blood cells (RI = 1.35~1.36) for human health and disease diagnosis. Full article
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<p>Cross-sectional schematic of graphene/Au/SiC waveguide SPR sensor structure.</p>
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<p>Confinement factor as a function of Au thickness. The number of graphene layers was 10. The RI of the sensing medium was 1.344. Inset: resonant peak at 675 nm with 50 nm thick gold.</p>
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<p>Resonance wavelength for graphene/Au/SiC sensor with different numbers of graphene layers. The gold thickness was 50 nm. The RI of the sensing medium was 1.344.</p>
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<p>Comparison of resonance wavelength shift for a Au/SiC (black curves, N = 0) and a graphene/Au/SiC (blue curves, N = 10) waveguide-based SPR sensor when the RI of the sensing medium changes from 1.33 (solid curves) to 1.36 (dashed curves).</p>
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<p>Resonance peak shift with the number of graphene layers. The gold thickness was 50 nm and RI ranges from 1.33 to 1.36.</p>
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12 pages, 4699 KiB  
Article
Novel Regeneration Approach for Creating Reusable FO-SPR Probes with NTA Surface Chemistry
by Jia-Huan Qu, Karen Leirs, Remei Escudero, Žiga Strmšek, Roman Jerala, Dragana Spasic and Jeroen Lammertyn
Nanomaterials 2021, 11(1), 186; https://doi.org/10.3390/nano11010186 - 13 Jan 2021
Cited by 11 | Viewed by 3509
Abstract
To date, surface plasmon resonance (SPR) biosensors have been exploited in numerous different contexts while continuously pushing boundaries in terms of improved sensitivity, specificity, portability and reusability. The latter has attracted attention as a viable alternative to disposable biosensors, also offering prospects for [...] Read more.
To date, surface plasmon resonance (SPR) biosensors have been exploited in numerous different contexts while continuously pushing boundaries in terms of improved sensitivity, specificity, portability and reusability. The latter has attracted attention as a viable alternative to disposable biosensors, also offering prospects for rapid screening of biomolecules or biomolecular interactions. In this context here, we developed an approach to successfully regenerate a fiber-optic (FO)-SPR surface when utilizing cobalt (II)-nitrilotriacetic acid (NTA) surface chemistry. To achieve this, we tested multiple regeneration conditions that can disrupt the NTA chelate on a surface fully saturated with His6-tagged antibody fragments (scFv-33H1F7) over ten regeneration cycles. The best surface regeneration was obtained when combining 100 mM EDTA, 500 mM imidazole and 0.5% SDS at pH 8.0 for 1 min with shaking at 150 rpm followed by washing with 0.5 M NaOH for 3 min. The true versatility of the established approach was proven by regenerating the NTA surface for ten cycles with three other model system bioreceptors, different in their size and structure: His6-tagged SARS-CoV-2 spike fragment (receptor binding domain, RBD), a red fluorescent protein (RFP) and protein origami carrying 4 RFPs (Tet12SN-RRRR). Enabling the removal of His6-tagged bioreceptors from NTA surfaces in a fast and cost-effective manner can have broad applications, spanning from the development of biosensors and various biopharmaceutical analyses to the synthesis of novel biomaterials. Full article
(This article belongs to the Special Issue Nanomechanical and Optical Biosensors)
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<p>Schematic concept for the regeneration of cobalt (II)-nitrilotriacetic acid (NTA) surface on a gold-coated fiber-optic (FO) sensor probe by reversible removal/immobilization of His<sub>6</sub>-tagged bioreceptors. Four different model systems have been tested to verify the concept, including His<sub>6</sub>-tagged scFv-33H1F7, receptor-binding domain (RBD), red fluorescent protein (RFP) and Tet12SN-RRRR. scFv-33H1F7 has been depicted in the regeneration cycle as one of the examples.</p>
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<p>(<b>a</b>) The fiber−optic−surface plasmon resonance (FO−SPR) sensorgram representing one regeneration cycle including (1, 3 and 6) immobilization buffer (TBS) stabilization, (2) formation of the Co(II)−NTA chelate, (4) immobilization of His<sub>6</sub>−tagged scFv−33H1F7 (at 20 μg/mL) and (5) removal of scFv−33H1F7 to regenerate the NTA surface following different regeneration conditions. The represented sensorgram was obtained using condition G. (<b>b</b>) The obtained baseline shifts after removal of scFv−33H1F7 following seven different regeneration conditions (conditions A to G, as detailed in <a href="#sec2dot3-nanomaterials-11-00186" class="html-sec">Section 2.3</a>). Each bar represents the average value of two parallel measurements performed on two different FO sensor probes, with error bars being standard deviations (n<sub>s</sub> = 2).</p>
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<p>The FO−SPR sensorgram representing ten regeneration cycles, including (1, 3 and 6) TBS stabilization, (2) formation of the Co(II)−NTA chelate, (4) immobilization of scFv−33H1F7 at 20 μg/mL and (5) removal of scFv−33H1F7 to regenerate the NTA surface using condition G. The baseline shift (blue arrows) for each cycle and the immobilization shift for cycle 1 and 2 (orange arrow) are depicted.</p>
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<p>(<b>a</b>) The baseline (blue) and immobilization (orange) shift obtained in different cycles. (<b>b</b>) The sum of the immobilization shift per cycle and the baseline shift from the preceding cycle (except for cycle 1, where only immobilization shift is depicted as there is no baseline shift prior to this cycle). Each bar represents the average value of two parallel measurements performed on two different FO sensor probes, with error bars being standard deviations of the overall shift (n<sub>s</sub> = 2).</p>
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<p>The baseline and immobilization shifts obtained for ten regeneration cycles, with His<sub>6</sub>−tagged scFv−33H1F7 immobilized at 20 μg/mL in each cycle. The FO sensor probe surface regeneration was performed using condition G, combined with different washing conditions: (<b>a</b>) 0.1 M NaOH for 5 min with or without shaking at 150 rpm and (<b>b</b>) 0.5 M NaOH for 1, 3 or 5 min without shaking. Each bar represents the average value from two parallel measurements performed on two different FO sensor probes, with error bars being standard deviations (n<sub>s</sub> = 2).</p>
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<p>The FO-SPR sensorgram obtained from two parallel FO probes representing ten regeneration cycles of His<sub>6</sub>−tagged scFv−33H1F7, including the following steps: (1, 3 and 7) TBS stabilization, (2) formation of the Co(II)−NTA chelate, (4) immobilization of scFv−33H1F7 at 20 μg/mL, (5) removal of scFv−33H1F7 and (6) washing with NaOH, using the optimized regeneration protocol (i.e., condition G combined with 3 min washing in 0.5 M NaOH).</p>
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<p>The FO−SPR sensorgrams obtained from two parallel FO probes representing ten regeneration cycles, performed using the optimized regeneration protocol (i.e., condition G combined with 3 min washing in 0.5 M NaOH), shown for different His<sub>6</sub>-tagged bioreceptor model systems: (<b>a</b>) RBD, (<b>b</b>) RFP and (<b>c</b>) Tet12SN−RRRR.</p>
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<p>The (<b>a</b>) baseline and (<b>b</b>) immobilization shifts for each cycle, obtained with immobilizing RBD, RFP and Tet12SN−RRRR at 20 μg/mL. The surface regeneration was performed using condition G and washing with 0.5 M NaOH for 3 min, for a total of ten cycles. Each bar represents the average value from two parallel measurements performed on two different FO sensor probes, with error bars being standard deviations (n<sub>s</sub> = 2).</p>
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13 pages, 3122 KiB  
Article
Development of a Portable SPR Sensor for Nucleic Acid Detection
by Yafeng Huang, Lulu Zhang, Hao Zhang, Yichen Li, Luyao Liu, Yuanyuan Chen, Xianbo Qiu and Duli Yu
Micromachines 2020, 11(5), 526; https://doi.org/10.3390/mi11050526 - 21 May 2020
Cited by 30 | Viewed by 3781
Abstract
Nucleic acid detection is of great significance in clinical diagnosis, environmental monitoring and food safety. Compared with the traditional nucleic acid amplification detection method, surface plasmon resonance (SPR) sensing technology has the advantages of being label-free, having simple operation, and providing real-time detection. [...] Read more.
Nucleic acid detection is of great significance in clinical diagnosis, environmental monitoring and food safety. Compared with the traditional nucleic acid amplification detection method, surface plasmon resonance (SPR) sensing technology has the advantages of being label-free, having simple operation, and providing real-time detection. However, the angle scanning system in many SPR angle modulation detection applications usually requires a high-resolution stepper motor and complex mechanical structure to adjust the angle. In this paper, a portable multi-angle scanning SPR sensor was designed. The sensor only uses one stepping motor to rotate a belt, and the belt pulls the mechanical linkages of incident light and reflected light to move in opposite directions for achieving the SPR angle scanning mode that keeps the incident angle and reflected angle equal. The sensor has an angle scanning accuracy of 0.002°, response sensitivity of 3.72 × 10−6 RIU (refractive index unit), and an angle scanning range of 30°–74°. The overall size of the system is only 480 mm × 150 mm × 180 mm. The portable SPR sensor was used to detect nucleic acid hybridization on a gold film chip modified with bovine serum albumin (BSA). The result revealed that the sensor had high sensitivity and fast response, and could successfully accomplish the hybridization detection of target DNA solution of 0.01 μmol/mL. Full article
(This article belongs to the Section B:Biology and Biomedicine)
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<p>(<b>a</b>) Schematic of angle modulation (Position 1); (<b>b</b>) schematic of angle modulation (Position 2).</p>
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<p>Real surface plasmon resonance (SPR) instrument set-up in this paper.</p>
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<p>Schematic illustration of the experimental protocol.</p>
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<p>Angle scanning curve of deionized water.</p>
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<p>Linear regression curves of unmodified gold film chip.</p>
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<p>Linear regression curves of gold film chip modified with bovine serum albumin (BSA).</p>
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<p>(<b>a</b>) Reaction curve of streptavidin (SA) binding to BSA; (<b>b</b>) reaction curves of DNA probes binding to SA.</p>
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<p>Reaction curves of DNA hybridization detection.</p>
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<p>Standard curve of target DNA sequences.</p>
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14 pages, 3135 KiB  
Article
Enhanced Biosensing Activity of Bimetallic Surface Plasmon Resonance Sensor
by Ritayan Kashyap, Soumik Chakraborty, Shuwen Zeng, Sikha Swarnakar, Simran Kaur, Robin Doley and Biplob Mondal
Photonics 2019, 6(4), 108; https://doi.org/10.3390/photonics6040108 - 21 Oct 2019
Cited by 34 | Viewed by 4817
Abstract
Surface plasmon resonance (SPR) sensors present a challenge when high sensitivity and small FWHM (full width at half maximum) are required to be achieved simultaneously. FWHM is defined by the difference between the two extreme values of the independent variable at which the [...] Read more.
Surface plasmon resonance (SPR) sensors present a challenge when high sensitivity and small FWHM (full width at half maximum) are required to be achieved simultaneously. FWHM is defined by the difference between the two extreme values of the independent variable at which the value of the dependent variable is equal to half of its maximum. A smaller value of FWHM indicates better accuracy of SPR measurements. Theoretically, many authors have claimed the possibility of simultaneously achieving high sensitivity and small FWHM, which in most of the cases has been limited by experimental validation. In this report, an experimental study on the improved surface plasmon resonance (SPR) characteristics of gold over silver bimetallic sensor chips of different film thicknesses is presented. A comparative study of antigen–antibody interaction of the bimetallic chip using a custom-made, low-cost, and portable SPR device based on an angular interrogation scheme of Kretschmann configuration is performed. Pulsed direct current (DC) magnetron-sputtered bimetallic films of gold over silver were used in the construction of the SPR chip. The FWHM and sensitivity of the bimetallic sensors were firstly characterized using standard solutions of known refractive index which were later immobilized with monoclonal anti-immunoglobulin G (IgG) in the construction of the SPR biochip. Spectroscopic measurements such as ultraviolet–visible light spectroscopy (UV–Vis) and Fourier-transform infrared spectroscopy (FTIR) were used for the confirmation of the immobilization of the antibody. The performance of the bimetallic SPR biochip was investigated by exposing the sensor to various concentrations of the target protein. The results indicated that the bimetallic sensors of silver/gold had a 3.5-fold reduced FWHM compared to pure gold-based sensors, indicating a higher detection accuracy. In addition, they exhibited a significant shift in resonance angle as high as 8.5 ± 0.2 due to antigen–antibody interaction, which was ~1.42-fold higher than observed for pure silver-based sensors. Full article
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<p>Representation of protein immobilization scheme.</p>
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<p>Representation of (<b>a</b>) the experimental set-up and (<b>b</b>) sensor measurement procedure.</p>
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<p>UV-Vis spectroscopic optical absorbance spectra of the sensor surface before and after immobilization of antibody.</p>
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<p>Transform Infrared spectra of the sensor surface before and after the immobilization of antibody: (<b>a</b>) absorbance vs wavenumber (2800–3000 cm<sup>−1</sup>), (<b>b</b>)absorbance vs wavenumber (1000–1800 cm<sup>−1</sup>).</p>
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<p>Data against standard test samples of water, acetone and hexane for sensors (<b>a</b>) Ag-I (<b>b</b>) Au-II (<b>c</b>) Ag-Au-III (<b>d</b>) Ag-Au-IV. Embedded figure plots the changes of resonance angle with the refractive index of the medium. Corresponding to a higher change in refraction index of the sample, the resonance happened at a higher angle of incidence.</p>
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<p>Reflectance vs. incident angle of stacked layers (test sensor: Ag-I test protein concentration: 0.1 mg/mL).</p>
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<p>Reflectance vs. incident angle curve of the sensor (<b>a</b>) Ag-I, (<b>b</b>) Au-I, (<b>c</b>) Ag-Au-III, (<b>d</b>) Ag-Au-IV towards different concentrations of protein (0.1 mg/mL, 0.4 mg/mL, 0.7 mg/mL, and 1 mg/mL).</p>
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<p>Graph of resonance angle with concentration of antibody protein exposed to sensor surface.</p>
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<p>Sensorgrams showing the binding kinetic with protein IgG of different concentrations for sensors: (<b>a</b>) Ag-I, (<b>b</b>) Au-II, (<b>c</b>) Ag-Au-III, (<b>d</b>) Ag-Au-IV.</p>
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7 pages, 254 KiB  
Editorial
Surface Plasmon Resonance (SPR) to Magneto-Optic SPR
by Conrad Rizal, Vladimir Belotelov, Daria Ignatyeva, Anatoly K. Zvezdin and Simone Pisana
Condens. Matter 2019, 4(2), 50; https://doi.org/10.3390/condmat4020050 - 27 May 2019
Cited by 23 | Viewed by 4879
Abstract
In this editorial, a brief background of the surface plasmon resonance (SPR) principle is discussed, followed by several aspects of magneto-optic SPR (MOSPR) and sensing schemes from the viewpoint of fundamental studies and potential technological applications. New sensitivity metrics are introduced that would [...] Read more.
In this editorial, a brief background of the surface plasmon resonance (SPR) principle is discussed, followed by several aspects of magneto-optic SPR (MOSPR) and sensing schemes from the viewpoint of fundamental studies and potential technological applications. New sensitivity metrics are introduced that would allow researchers to compare the performance of SPR and MOSPR-based sensors. Merits of MOSPR over SPR based sensors and challenges faced by MOSPR sensors in terms of their practical use and portability are also considered. The editorial ends with potential new configurations and future prospects. This work is considered highly significant to device engineers, graduate and undergraduate students, and researchers of all levels involved in developing new classes of bio-devices for sensing, imaging, environmental monitoring, toxic gas detection, and surveying applications to name a few. Full article
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Figure 1

Figure 1
<p>Comparison of the SPR and MOSPR sensitivities for two systems denoted by A and B.</p>
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