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12 March 2012 Polarization-interferometry-based wavelength-interrogation surface plasmon resonance imager for analysis of microarrays
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Abstract
Polarization interferometry (PI) techniques, which are able to improve surface plasmon resonance (SPR) sensing performance and reduce restrictions on allowable parameters of SPR-supporting metal films, have been experimentally realized only in SPR sensors using monochromatic light as a source. Wavelength-interrogation SPR sensors modulated by PI techniques have not been reported due to the wavelength-sensitive characterization of PI phase compensators. In this work we develop a specially designed rhombic prism for phase compensating which is totally insensitive to wavelength. For the first time we successfully apply PI technique to a wavelength-interrogation SPR imager. This imager is able to offer two-dimensional imaging of the whole array plane. As a result of PI modulation, resolutions of 1.3×10−6 refractive index unit (RIU) under the normal condition and 3.9×10−7 RIU under a more time-consuming condition are acquired. The application of this imager was demonstrated by reading microarrays for identification of bacteria, and SPR results were confirmed by means of fluorescence imaging.

1.

Introduction

Microarray technology, which facilitates sensing of multiple biomolecular interactions in parallel, has revolutionized the biomedical research since its advent in the end of the 20th century.1,2 A well-known approach to microarray analysis in a label-free and real-time manner is the surface plasmon resonance (SPR) method.3,4 There are three main configurations used in SPR sensors: amplitude measurement, phase modulation, and spectroscopy-based measurement.5 Amplitude measurements are based on a relationship between the change in reflective light intensity and the refractive index of bound analyte.6 Because they are based on direct intensity variations, amplitude measurements are vulnerable to stray light and spatial inhomogeneity in the light source.7 SPR sensors based on phase modulation make use of the phase shift when SPR occurs.8,9 Although these sensors have exhibited high sensitivity, they suffer from the instability of the complicated setup and the limited dynamic range.10 Spectroscopy-based measurements include two modes: wavelength interrogation and angular interrogation. They measure the reflectivity as a function of the incident angle (angular mode) or wavelength (wavelength mode). Owing to the acquisition of the complete resonance curve, spectroscopy-based measurements offer better signal-to-noise ratio compared with the other configurations.7 During the past years, some wavelength-interrogation SPR sensors have been described in the literature.7,1113 Yuk et al. proposed a wavelength interrogation-based SPR biosensor for analysis of protein interactions on protein arrays;12,13 however, the point-by-point scan mode limited the detection throughput. Bardin et al. presented an SPR spectro-imaging system introducing an additional spatial dimension.7 This system is based on the illumination of a biochip through a vertical slit, and thus it can only be applied to analysis of linear multi-spot arrays due to the slit diffraction. We formerly reported a parallel scan wavelength-interrogation SPR imager which line-focused the light for signal excitation and was able to provide two-dimensional imaging of the whole array plane with a high throughput.11 However, the sensing performance of this imager was in need of improvement.

Many efforts are currently devoted to the improvement of SPR sensing performance. It is well-known that SPR performance strongly depends on the quality of metal films, e.g., thickness and homogeneity. In theory, the minimum of SPR reflectivity can be zero, i.e., the contrast of SPR intensity profile can be infinity with an appropriate film thickness. However, the metal films can hardly satisfy optimum conditions due to the following reasons. Firstly, errors from the optimum thickness occur in the prepared metal films by magnetron sputtering or evaporation coating. Secondly, the biomolecular layer immobilized on the metal film can change the optimum thickness. Usually the properties of these biomolecules remain unknown, and thus the optimum film thickness can not be predicted the oretically. In order to overcome the above-mentioned problems, a phase-polarization contrast method called polarization interferometry (PI) has been proposed and applied to SPR biosensors.14 PI techniques make use of the phase difference between two polarization components and enables one to lower the minimum of reflected intensity nearly to zero. Owing to the PI technique, films with non-optimum SPR coupling thicknesses can achieve good sensing performance, and the restrictions on allowable parameters of SPR-supporting metal films are reduced. At present, the PI technique has been experimentally realized in SPR systems with a monochromatic light source.10 However, the realization of PI technique in wavelength-interrogation SPR sensors, which use white light as a source, still poses significant challenges because the critical optic of PI technique—the phase compensator—is extremely sensitive to wavelength.

In this work we design a new optic as the phase compensator which is based on the differences in the phase shift between s- and p- components when reflecting (s- or p- polarization means that the electric field of the light wave lies vertically to or just in the incidence plane, respectively). Different from conventional phase compensators, it is totally insensitive to wavelength. As a result, we successfully applied it to spectroscopic SPR systems and developed a PI based wavelength-interrogation SPR imager for analysis of microarrays. This paper is organized as follows: Firstly, the principle and experimental realization of PI techniques are presented. In particular, the optical design of this wavelength-insensitive phase compensator is discussed in detail. Secondly, system characterization of this PI based, parallel scan spectroscopic SPR imager was carried out. Detailed results are presented, including measurements of the refractive index resolution, the spatial resolving power, as well as the detection limit. Finally, a microarray experiment for identification of bacteria was conducted to demonstrate the biomedical application of this imager, and SPR results were further confirmed by fluorescence imaging.

2.

Materials and Methods

2.1.

Polarization Interferometry

Polarization interferometry (PI) technique exploits the phase difference between two polarization components to lower the minimum of the SPR dip and then increase the accuracy of the resonance-wavelength shift measurements.14 Figure 1 shows the schematic of PI technique. Polarizer 1 is used to adjust the amplitude of s- and p- polarized components, in order that they have nearly the same amplitude when they pass through the SPR module. The phase compensator adjusts the phase difference between s- and p- components, in order that the resulting reflected wave after the phase compensator is polarized linearly at the SPR minimum. The amplitude E of the reflected wave is a vector sum of s- and p- polarized components. If polarizer 2 is placed perpendicular to E, in theory, the exit intensity minimum would be zero, and the value of SPR contrast would be infinity. In actuality, the intensity minimum can hardly achieve zero exactly due to the non-idealities in the system.

Fig. 1

Optical design of polarization interferometry.

JBO_17_3_036002_f001.png

Ordinarily, a quarter-wave plate is used as the phase compensator in an angle-interrogation SPR sensor which uses a single wavelength as the light source. However, as the quarter-wave plate is extremely sensitive to the wavelength, it can hardly be used for PI modulation in a wavelength-interrogation SPR system with a broadband light source. Figure 2 shows the phase difference between two polarization components passing through a 633 nm quarter-wave plate versus wavelength. It reveals that the phase difference value differs from 90 deg significantly if the wavelength deviates from 633 nm. The refractive index information used for drawing this plot is acquired from the research by Ghosh et al.15 As far as we know, PI techniques have not yet been realized in a wavelength-interrogation SPR system as a result of wavelength dependence.

Fig. 2

Phase difference between two polarization components passing through a 633 nm quarter-wave plate versus wavelength.

JBO_17_3_036002_f002.png

In this work, we propose a unique method of phase compensating which is insensitive to wavelength. Such a phase compensating method is based on the differences in the phase shift between s- and p- polarization components. If the light passes from dielectric 1 to dielectric 2 (n1>n2) at an angle equal to or larger than the angle of total reflection, the phase shifts of reflected p- and s- components can be expressed by Eqs. (1) and (2),

Eq. (1)

δp=2tan1n1n2[(n1/n2)2sin2θ1]1/2cosθ,

Eq. (2)

δs=2tan1n2n1([n2/n1)2sin2θ1]1/2cosθ,
where n1 and n2 are refractive indices of dielectric 1 and dielectric 2, respectively, and θ is the angle of incidence. According to the phase shifts, we designed and fabricated a rhombic prism for phase compensation, as shown in Fig. 3(a). It is demonstrated that the light beam undergoes two reflecting processes when it passes through this prism. In order that the rhombic prism can be used as a wavelength-insensitive quarter-wave compensator, the total difference Δ which can be expressed as two times of |δpδs|, should satisfy the following matching condition:

Eq. (3)

Δ=2|δpδs|=π/2.
We choose BK7 glass as the material for fabrication of prism, whose refractive index is 1.51322 refractive index units (RIU) at 633 nm.15 According to Eqs. (1), (2) and (3), θ is calculated to be 55.05 deg. Then we investigate the wavelength dependence of this prism. As can be seen from Fig. 3(b), the phase difference varies slightly with the changing wavelength, revealing that the newly developed rhombic prism can be successfully applied to a wavelength-interrogation SPR system for phase compensation.

Fig. 3

Optical design and performance of the wavelength-insensitive rhombic prism. (a) Configuration of the prism. (b) Phase difference between two polarization components passing through the prism versus wavelength.

JBO_17_3_036002_f003.png

2.2.

Imaging Systems Design

Figure 4 shows the schematic of the polarization interferometry based, parallel scan, wavelength interrogation SPR imager. As introduced in the last section, polarizer 1 in the incidence arm, and phase compensator as well as polarizer 2 in the emergence arm, form the main optics of PI technique. In this system, a halogen lamp with a power of 100 W is used as the light source. The broadband light is focused by a 10×objective (lens 1) on an aperture and then collimated by lens 2. Then, cylindrical lens 1 focuses the light to a line on the surface of the microarray. In our system, the SPR module is configured in a Kretschmann manner with an attenuated total reflection method: a gold film is placed on the surface of a BK7 prism using a droplet of refractive index matching liquid (n:1.51481.5152RIU) to avoid entrapment of air-bubbles. The sensing layer is the surface of the gold film, where arrays of genetic elements are printed. The prism is fixed on a translation stage that enables a one-dimensional parallel scan. In the emergence arm, the reflected light beam is collimated by cylindrical lens 2. Then cylindrical lens 3 is placed to image the pattern of the sample, irradiated by the focused line light, to the entrance slit of a spectrometer. A charge coupled device (CCD) camera records the spectrally resolved images for further data analysis.

Fig. 4

Schematic representation of this polarization interferometry based, wavelength-interrogation SPR imager.

JBO_17_3_036002_f004.png

2.3.

Fabrication of Microarrays

For the fabrication of DNA arrays, the magnetron sputtering gold films with a thickness of approximately 45 nm are used as substrates. The gold film needs to be cleaned thoroughly before the printing of sample spots. Firstly, the gold film is cleaned with a solution consisting of H2O2 (30%), NH3 (30%), and deionized water in a 1:1:5 ratio for 10 min.16 Then, the film is dipped into acetone and ethanol for 10 min oscillating successively. After that, the film is thoroughly rinsed by deionized water and then dried for array printing.

Throughout this study, we print DNA-probe arrays manually. The DNA strands were thiolated for covalent bonding to gold films. After the printing process, the prepared array-chip, kept in a wet box, was then put into the electric heating constant temperature incubator (Shanghai Permanent Science and Technology the Limited Company, DHP-9052) for 2 h immobilization at 37 °C. Then, the chip was rinsed with deionized water to remove unbound DNA strands. The DNA-probe arrays can be used for system characterization or further hybridization with target genes for biomedical applications.

2.4.

Spectral Data Analysis

Figure 5(a) shows an SPR sensing model with two spots of DNA strands printed on the substrate. Figure 5(b) is one of spectrally resolved images, corresponding to a certain position during optical scan. In this image, each row represents the SPR spectrum of one point on the irradiated line region. As can be seen, there is a certain pixel with minimum intensity in each row, corresponding to the resonance wavelength when SPR occurs. In this way, we acquire the resonance wavelength of every point in this illuminated line region, as shown in Fig. 5(c). By analysis of all the images acquired during parallel scan, the distribution of resonance wavelengths of the whole array can be obtained. According to the relationship between the resonance wavelength and the refractive index, finally the array plane can be characterized by different refractive indices. In this way, the detection signals of the whole array plane, in terms of refractive index, are acquired for further biomedical analysis.

Fig. 5

Spectral data analysis. (a) Design of the array. (b) One of dispersed images corresponding to a certain line region. (c) Distributions of the resonance wavelength of the scanned line region.

JBO_17_3_036002_f005.png

2.5.

Fluorescence Imaging

In order to validate the biomolecular interactions on microarrays, the array chip is carefully removed from the SPR module and placed on the scan stage of a fluorescence imaging system after completion of the SPR experiment.17 We have previously developed a quasi-confocal, hyperspectral fluorescence imaging system which provides accurate analysis of fluorescence-labeled microarrays.18 The SPR and fluorescence results are compared and discussed.

3.

System Characterization

3.1.

Results of PI Modulation

Figure 6(a) shows a comparison of SPR curves without (curve 1) and with (curve 2) PI modulation. We acquire these SPR curves, detecting air around the sensing plane, with a piece of magnetron-sputtering gold film with a thickness of 38 nm. The film thickness is a little different from the optimized thickness of approximately 45 nm when detecting air. We choose 38 nm for illustration here because in practice it is difficult to pre-set the film thickness at the optimum, due to complicated experimental conditions and difficulties of precise film-coating process control. As can be seen from Fig. 6(a), the minimum intensity decreases significantly as a result of PI modulation. The marked area is enlarged, as shown in the inset of Fig. 6(a). It is revealed from the inset that the noise fluctuation is also reduced by use of the PI technique. That is because the photon noise of the CCD camera is reduced with the decreasing of the incident intensity.

Fig. 6

A comparison of SPR results without and with the modulation of polarization interferometry. (a) A comparison of SPR curves. (b) SPR image without polarization interferometry. (c) SPR image with polarization interferometry.

JBO_17_3_036002_f006.png

It is also demonstrated from Fig. 6(a) that there is a wavelength shift of the intensity minima from without PI to with PI, which results from the non-idealities of PI-comprising optics.14 However, the phenomenon of wavelength shift after PI applies to all the points of the sensing plane. Strictly speaking, the relative shift of the resonance wavelength, not the absolute wavelength value, makes sense in the wavelength-interrogation SPR detection. If we choose a certain sample (such as air or water) as the refractive index reference, the absolute value of refractive index would not be affected. As a result of PI modulation, the restrictions on allowable parameters of SPR-supporting metal films and biomolecular layers are reduced.

The effect of the PI technique is also shown in the scanning image of an array-chip. The SPR images of 2×5 DNA-probe arrays without and with PI modulation are shown in Figs. 6(b) and 6(c), respectively. By comparing these two images, it is revealed that the image quality of SPR results has been improved as a result of PI modulation, although the improvement observed from these two images is not quite obvious. Sometimes the concentration of analyte could be very low in real samples, and therefore a slight improvement in signal-to-noise ratio could make a significant difference.19,20 The noise in the SPR system limits how small a change in refractive index can be reliably distinguished.20 By employing the PI technique, the noise is efficiently suppressed, and the signal-to-noise ratio is enhanced as a result,21 providing the potential of SPR biosensors for detecting analytes with extremely low concentrations.20,22

3.2.

Refractive Index Resolution

The calculation of refractive index resolution is shown in Eq. (4),23

Eq. (4)

δn=σ/Sn,
where δn is refractive index resolution, σ is standard deviation of SPR signal and Sn is the sensitivity of the system. For a wavelength-interrogation SPR system, sensitivity represents the relationship between the resonance wavelength and refractive index. The experiment will be carried out in the atmospheric environment, and thus we tested the sensitivity with the bare gold film naked in air. We changed the pressure of air around the SPR module step by step, so that refractive index of air varied with the changing pressure. Then we recorded the change of resonance wavelength that corresponds to the varying refractive index. The experimental results are shown in Fig. 7(a), and a sensitivity of 1.03×104nm/RIU is acquired. Then, we tested standard deviation σ of this wavelength-interrogation SPR system by detecting the resonance-wavelength fluctuations of air around the gold film. In order to make a comparison of sensing performance without and with PI modulation, both results are obtained, as shown in Figs. 7(b) and 7(c). The pressure, temperature, and humidity of air were maintained throughout the detection period. The experimental results demonstrate that the standard deviation of the PI-based system is much lower than that of the same system without application of PI technique, revealing that the PI technique contributes to the improvement of sensing performance. To further reduce noise level, we applied an image averaging method to data analysis. For an ideally independent noise with normal statistical distribution, the average of n images results in a decrease in the standard deviation by a factor of n (Ref. 9). Figure 7(d) shows the fluctuations, corresponding to the same data as shown in Fig. 7(c), with neighbored 10 images averaged, and a standard deviation of 0.004 nm is acquired. Typically, the acquisition time per image is 1 sec. By using the image averaging method, the reduction of noise is at the expense of acquisition time, and thus a reasonable averaging number should be chosen according to the detection demand. According to Eq. (4), refractive index resolutions of 1.3×106 RIU under the normal condition and 3.9×107 RIU under this time-consuming condition are obtained from this system. The latter is comparable to the best reported in literature,5 offering this system enormous potential for sensitive and accurate analysis of microarrays.

Fig. 7

The refractive index resolution of this imager. (a) The relationship between the resonance wavelength and refractive index. (b) SPR wavelength fluctuations acquired without polarization interferometry. (c) SPR wavelength fluctuations acquired with polarization interferometry. (d) Fluctuations of the same data in (c) with neighboring 10 images averaged.

JBO_17_3_036002_f007.png

3.3.

Spatial Resolution and Detection Limit

To test the spatial resolution of this system, we prepared a piece of gold film with patterns of ultrathin lines using a laser marking machine. Figure 8 shows the SPR image of the sensing plane. The center-to-center spacings of these vertical lines are approximately 75 µm, and that of these horizontal lines are approximately 85 µm. All the lines in this image can be clearly resolved, indicating that the spatial resolution of our system is better than 100 µm. The spot diameters and center-to-center spacings of typical microarrays are of the order of 100μm; thus, the spatial resolving power of this system is adequate for microarray analysis.

Fig. 8

The spatial resolution of this imager. Center-to-center line spacing is 75 µm for the vertical lines (left) and 85 µm for the horizontal ones (right).

JBO_17_3_036002_f008.png

In SPR sensing, the detection limit is always demonstrated by detecting bacterial cells. Here the bacteria used are Escherichia coli DH-5α. The gold coated substrates are firstly immersed in a solution of 16-mercaptohexadecanoic acid (1 mM) for 12 h for the obtaining of a dense self-assembled monolayer. The terminal carboxylic group is activated by EDC (1-ethyl-3- (3-dimethylaminopropyl) carbodiimide hydrochloride)/NHS (N-Hydroxysuccinimide) chemistry. The substrate was immersed in a solution of 0.4 mM EDC-0.1 mM NHS in reaction buffer (2- (N-morpholino) ethanesulfonic acid 20.62 g/L, NaCl 29.2 g/L) for 30 min, and then a solution of 10 μg/ml of anti-E. coli DH-5α antibody was incubated over the substrate surface for 1 h. The non-specific sites were blocked by incubation with 0.1% bovine serum albumin (BSA) for 40 min. Then different concentrations of diluted E. coli DH-5α, ranging from 104107cfu/mL (colony-forming units per milliliter), were successively dropped onto the surface, and the detection results are shown in Fig. 9. Furthermore, these curves near the resonance wavelength are enlarged and shown in the inset. The resonance wavelengths corresponding to the solutions of diluted E. coli DH-5α (104107cfu/mL) were 719.0, 719.5, 720.3, and 721.7 nm, respectively. The experimental data reveal that the increase of E. coli concentration leads to that of resonance wavelength, which could be attributed to the specific recognition of bacteria with the antibody. We acquire a detection limit of 104  cfu/mL with a good repeatability, which is comparable to the reported values in the literature.2426

Fig. 9

SPR curves corresponding to immobilized antibody and different concentrations of Escherichia coli for determining the detection limit of this imager.

JBO_17_3_036002_f009.png

4.

Biomedical Application of Microarrays

The identification of bacteria by imaging gene chips is performed by this spectroscopic SPR imager as an example of biomedical applications of microarrays. In order to confirm the SPR results, these array-chips are imaged by a fluorescence imaging system after completion of SPR experiments. The complementary target genes were labeled with fluorescent dyes, in order that the hybridized arrays can provide both SPR and fluorescence signals. Throughout this study, Cy5 (absorption/emission: 649/667nm) and Dylight 680 (absorption/emission: 680/715nm) were used as fluorescent labels. Both the DNA probes and fluorescence-labeled target genes are purchased from TaKaRa Biotechnology (Dalian, China).

In this experiment, the DNA fragments were labeled with fluorophores to validate SPR results. Therefore, we carried out a test before this experiment to investigate whether fluorophores affect SPR results. We prepare an array-chip with 6 spots of DNA probes with the same concentration of 0.1μmol/L. The left 3 spots are label-free, while the other 3 spots are labeled with Cy5. The SPR results are shown in Fig. 10(a), and the refractive index graph of the marked row in Fig. 10(a) is shown in Fig. 10(b). As can be seen, the values of refractive index of these 6 spots are nearly identical. Figure 10(c) shows the corresponding fluorescent images. Our experiment with Dylight 680 shows similar results (data not shown). These imaging results demonstrate that the labeled fluorophores have little influence in the SPR results, providing the potential for subsequent validation experiments.

Fig. 10

SPR and fluorescent results with both label-free spots (left 3) and spots labeled with Cy5 (right 3). (a) SPR image of the array-chip. (b) Refractive index graph of the marked row in (a). (c) Corresponding fluorescent image of the array-chip.

JBO_17_3_036002_f010.png

Then we carried out the experiment of DNA hybridization. The gold-film-covered quartz is used as the substrate, where four 4×5 probe arrays were printed manually. As shown in Fig. 11(a), the array comprises one row of β-hemolytic streptococcus probes [5′(SH)-T18ACCGTCACTTGGTGGATT-3′] with a concentration of 2μM, one row of Escherichia coli probes [5′(SH)-T18ACGGTTACCTTGTTACGACTT-3′] with a concentration of 2μM, one row of non-specific DNA sequence as negative control (5′(SH)-T18AGAAGCAAGCTTCTCGTCCG-3′) which can be served as quality report marks of the chip hybridization, and one row of positive probes [fluorescence labeled probe DNA strands: [5′(SH)-T18AGAGTTTGATCCTGGCTCAG-3′(Cy5)] with a concentration of 5μM. The repetition of the same 5 spots in each row is used to demonstrate the credibility of the experiment.

Fig. 11

Identification of bacteria as an example of biomedical applications of microarrays. (a) Design of the array. Scanning results with (b) no microbe, (c) only β-hemolytic streptococcus, (d) both two microbes, and (e) only Escherichia coli DNA fragments in the sample solution. The top images show SPR results, and the bottom images show fluorescence results as confirmations of SPR results.

JBO_17_3_036002_f011.png

Then the probe arrays were hybridized with different kinds of sample solutions, and imaged by SPR and fluorescence systems, respectively. The top images in Figs. 11(b)11(e) show the SPR results. Figure 11(b) shows the detection results with no microbe DNA fragments present in the sample solution. As expected, only the positive probes report a high signal. If the complementary Escherichia coli DNA sequence is present in a sample, then the row of Escherichia coli probes will show a high signal. Similarly, the row of β-hemolytic streptococcus probes will show a high signal if β-hemolytic streptococcus is present in the sample. As can be seen from Figs. 11(c) and 11(e), the SPR results correspond well with expectation. Figure 11(d) shows the results with both Escherichia coli and β-hemolytic streptococcus in the sample, and then all the rows of probes, except the row of negative probes, show a high signal.

After acquisition of SPR results, these arrays were carefully removed to the scan stage of a fluorescence imaging system. Fluorescence signals of these arrays were acquired to confirm SPR results. Fluorescent dye of Cy5 was labeled to positive and Escherichia coli DNA fragments, and Dylight 680 was used for β -hemolytic streptococcus. Colors of red and blue represent different dyes. The bottom images in Figs. 11(b)11(e) show the fluorescence imaging results. As expected, a certain row of probes will show a high fluorescent intensity signal if the corresponding microbe DNA fragments are present in the sample, otherwise these rows will show a low (or zero) signal, revealing that the target genes are selectively hybridized to the chip-bound probes. As can be seen from these images, fluorescence results correspond well with SPR results, indicating that the proposed SPR imager can be successfully applied to biomedical research.

5.

Conclusions

In this work, we have proposed a polarization-interferometry-based, wavelength-interrogation SPR imager. By developing a wavelength-insensitive rhombic prism as the phase compensator, we successfully apply a PI technique to a wavelength-interrogation SPR system. As a result of PI modulation, combined with the use of a fit algorithm, the sensing performance is greatly improved. A refractive index resolution of 1.3×106RIU is acquired under the normal condition, and an improved resolution of 3.9×107RIU is obtained with neighboring 10 images averaged. Such a resolution achieves the best performance level of SPR sensors using conventional surface plasmons. This system employs a pushbroom scan architecture that line-focuses the excitation light on the array plane, and records the complete SPR curve for every voxel of the plane by parallel scan of the line light. In this way, the detection throughput is greatly improved compared with mono-channel SPR sensing systems, making this imager particularly suitable for analysis of microarrays. A spatial resolution better than 100 µm and a detection limit of 1044  cfu/mL of Escherichia coli bacteria were acquired from this system, which is adequate for microarray detection. The application of this SPR system is demonstrated by reading microarrays for identification of bacteria, and the SPR results are in accordance with the fluorescence results. We believe that the proposed polarization interferometry based SPR imager could be used to build a commercially valuable instrument for biomedical research.

Acknowledgments

This research was made possible with the financial support from NSFC China (grants 81171375), Program for New Century Excellent Talents in University and Shenzhen Science Fund for Distinguished Young Scholars (2010).

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© 2012 Society of Photo-Optical Instrumentation Engineers (SPIE) 0091-3286/2012/$25.00 © 2012 SPIE
Zhiyi Liu, Heng Shi, Xinyuan Chong, Suihua Ma, Jihua Guo, Hui Ma, Yonghong He, Le Liu, Xiaoxiao Wang, and Yanhong Ji "Polarization-interferometry-based wavelength-interrogation surface plasmon resonance imager for analysis of microarrays," Journal of Biomedical Optics 17(3), 036002 (12 March 2012). https://doi.org/10.1117/1.JBO.17.3.036002
Published: 12 March 2012
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