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Duan Ruiqi, Yu Xiuzhang, Lan Zhu, et al. Research progress in applications of LSPR biosensor for clinical medicine detection[J]. Opto-Electronic Engineering, 2017, 44(2): 152-160. doi: 10.3969/j.issn.1003-501X.2017.02.003
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Research progress in applications of LSPR biosensor for clinical medicine detection
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Abstract
Tumor biomarker plays an important role in early diagnosis, treatment evaluation, and prognosis prediction for human medicine and cancers. At present, the human serum tumor biomarker detection methods mainly include radioimmunoassay (RIA), enzyme linked immunosorbent assay (ELISA), and chemiluminescence immunoassay (CLEIA), which have disadvantages of radioactive contamination, complicated operation, and long detection time and high cost. Various issues exist in these methods which limit its widespread applications in clinic screening. Recently, biosensors based on localized surface plasmon resonance (LSPR) have attracted much research attention for their remarkable superiority in the domain of biomedicine detection. The LSPR biosensor, a novel type of optical fiber-based biosensor, uses an optical fiber or optical fiber bundle to transform biological recognition information into analytically useful signals in the LSPR spectrum, which is suitable for clinical detection because of the advantages of high sensitivity, high specificity, label free, portable equipment and lower cost. However, up to now, there was little progress on the report of the detection of tumor biomarkers associated diseases and tumors by using this LSPR biosensor. In this paper, the principle and research progress of local surface plasmon resonance biosensor, as well as the main findings of our study in the detection of tumor markers are reviewed.-
Keywords:
- localized surface plasmon resonance /
- biosensor /
- clinical medicine /
- tumor biomarker
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References
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Overview
Abstract: Tumor biomarker plays an important role in early diagnosis, treatment evaluation, and prognosis prediction for human medicine and cancers. At present, the human serum tumor biomarker detection methods have defections, such as radioactive contamination, complicated operation, long detection time and high cost, which limit the widespread applications in clinic screening. The LSPR biosensor, a novel type of optical fiber-based biosensor, uses an optical fiber or optical fiber bundle to transform biological recognition information into analytically useful signals in the LSPR spectrum, which is suitable for clinical detection because of the advantages of high sensitivity, high specificity, label free, portable equipment and lower cost. In this paper, the principle and research progress of local surface plasmon resonance biosensor, especially the main findings of our study group, are reviewed.
In this work, the physical characteristics of metal nanostructure were calculated and simulated by discrete dipole approximation (DDA). Combining with reactive ion etching (RIE), nanosphere lithography (NSL) was applied to produce the triangle nanostructures. Eventually, a triangle silver nanostrure array with high refractive index sensitivity was produced. Meanwhile, a primitive ultraviolet-visible spectrometer was constructed to make spectro-analysis. An effective biological sensitive layer was fabricated on the surface of nanostructures by means of 11-mercaptoundecanoic acid (MUA) amine couple method.
To explore the clinical applications of this LSPR biosensor, we firstly used it to detect the microalbuminuria. The anti-human albumin antibody was immobilized on the sensor surface. Different concentrations of commercial albumin and albumin in urine samples from patients were determined according to the peak of LSPR extinction spectra. The biosensor displayed a detection limit of 1 ng/ml and wide dynamic range from 1 ng/ml to 1 mg/ml. Secondly, the anti-HE4 antibody as a probe, which could distinctly recognize HE4, an important ovarian tumor marker, was effectively assembled onto the nanochip surface. Human serum samples were detected and compared using an enzyme-linked immunosorbent assay. The linear range was between 10 pM and 10000 pM, with a detection limit of 4 pM and an excellent correlation between it and enzyme-linked immunosorbent assay. Thirdly, we made a functionalized chip surface with monoclonal anti-SCCa antibodies on the silver nanoparticles for distinct detection of SCCa. Different concentrations of SCCa were successfully tested in both buffer and human serum, with a linear quantitative detection range of 0.1~1000 pM. Lastly, the specific DNA probe was immobilized on the nanochip surface. Wild-type and mutant p53 DNA was detected. The low detection limit was 10 nM, with a wide dynamic range (10 nM~10 μM). Importantly, this sensor could effectively discriminate against single base mutations. By comparing with traditional methods, the advantage of the LSPR biosensor, such as wider detection range, label free, simple operation and short time was clear. It could provide a promising platform for developing clinical diagnostic applications.
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Duan Ruiqi, Yu Xiuzhang, Lan Zhu, et al. Research progress in applications of LSPR biosensor for clinical medicine detection[J]. Opto-Electronic Engineering, 2017, 44(2): 152-160. doi: 10.3969/j.issn.1003-501X.2017.02.003
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Figure 1.
Schematic principle of LSPR sensor [7].
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Figure 2.
Analysis of human CSF samples using a sandwich assay and the LSPR nanosensor[16]. (a) Surface chemistry for the possible ADDL detection in human CSF samples using the antibody "sandwich"assay. (b) Aging patient: LSPR spectra for each step of the assay. Ag nanoparticles after functionalization with 100 nM anti-ADDL (100 mM EDC) (B1), CSF (B2), 100 nM anti-ADDL (B3). (c) AD patient: LSPR spectra for each step of the assay. Ag nanoparticles after functionalization with 100 nM anti-ADDL (100mM EDC) (C1), CSF(C2), 100 nM anti-ADDL (C3). All measurements were collected in a N2 environment.
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Figure 3.
(a) Camera imaging of a 25 mm glass slide patterned with discrete circular regions of randomly ordered cylindrical nanoparticle arrays using a shadow mask. (b) Schematic showing randomly ordered nano-cylinder arrays within each circular region on the glass slide [18].
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Figure 4.
Design of LSPR nanobiosensor for albumin detection [26]. (a) Glass substrate. (b) Surface-confined sliver nanoparticles were synthesized using NSL. (c) The nanoparticles were incubated in MUA solution to form a SAM. (d) The substrates were incubated in EDC/NHS. (e) Anti-albumin antibody (10 mg/ml) immobilized the substrate. (f) Varying the concentrations of the albumin or the samples on the substrates completed the albumin immunoassay.
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Figure 5.
Test platform for extinction spectrum experiment.
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Figure 6.
Specific LSPR extinction spectrum for 1μg/ml albumin detection [26]. A: Ag nanoparticles before chemical modification. B: MUA (1 mM). C: EDC/NHS solution. D: antibody (10 mg/ml). E: albumin (1 mg/ml). All spectra were collected in air.
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Figure 7.
Specific LSPR extinction spectrum for patient albumin detection [26]. A: Ag nanoparticles before chemical modification. B: antibody. C: clinical sample. All spectra were collected in air environment.
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Figure 8.
Specific LSPR extinction spectrum for 100 pM SCCA detection [31]. A: Bare silver nanochip. B: Modification of 1 mM MUA. C: Incubation with 10 μg/mL monoclonal anti-SCCa. D: Detection of 100 pM SCCa.
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Figure 9.
Specific LSPR extinction spectrum for HE4 detection [36]. A: Bare silver nanochip. B: 1 mM 11-mercaptoundecanoic acid. C: functionalized biosensor with 10 μg/mL antibody. D: 500 pM HE4.
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Figure 10.
(a) Triangular Ag nanoparticles were fabricated on a glass substrate using NSL. (b) The nanoparticles were modified with MUA to form a SAM. (c) Amine-terminated DNA probes were immobilized on the MUA-coated nanoparticles with EDC/NHS activation. (d) Target DNA was hybridized with the immobilized probe.
