Skip to main content

Two-Dimensional Hole-Array Grating-Coupling-Based Excitation of Bloch Surface Waves for Highly Sensitive Biosensing


In this study, a surface diffraction two-dimensional (2D) grating structure was placed on the topmost layer of distributed Bragg reflectors (DBRs) for biosensing. Bloch surface wave (BSW) resonance was realized by coupling a 2D subwavelength hole-array grating and could be excited at different locations: the surface of 2D-grating layer or the inter-face between the DBR and bio-solution. Material losses in the multilayer dielectric were measured to test the robustness of this scheme. Both the surface diffraction-grating BSW (DG-BSW) and the alternative guided grating-coupled BSW (GC-BSW) configuration showed markedly enhanced angular sensitivity compared to conventional prism-coupled schematics. Exciting these modes using a grating-coupling technique appears to yield different extreme sensitivity modes with a maximum of 1190°/RIU for DG-BSW and 2255°/RIU for GC-BSW. Refractive index sensors with a high figure of merit may be realized via such compact configurations.


Specially designed photonic devices represent the possibility of real-time, label-free selective detection of various chemical and biological species for a variety of medical research and environmental monitoring applications and particularly for the optical detection of miniscule quantities of molecules in highly diluted solutions [1,2,3]. Optical surface mode resonance indices such as surface plasmon polaritons (SPPs) [4,5,6], microcavity [7], guided-mode resonance [8, 9], and Bloch surface waves (BSW) [10,11,12,13] can be utilized to distinguish the generally small modulations of optical parameter(s) reflective of a given biomolecule concentration [14, 15].

The most popular surface wave resonance-based sensing technology is the surface plasmon resonance (SPR) method [4, 16] which works by exciting surface plasmon polaritons along a metal/dielectric interface by incident light. Unfortunately, SPR can only be excited by transverse-magnetic light and absorption accompanied by strong dispersion is inevitable in the metal components. The sensitivity of the SPR biosensors is generally in the order of several hundred nanometers per refractive index unit (nm·RIU−1) [17, 18].

BSW is a promising alternative to SPPs. BSW technology based on the low optical loss all-dielectric structure has higher sensitivity and adjustable field enhancement than other surface waves and can be combined with different chemical surface modification methods and optical detection mechanisms [19,20,21]. Many researchers have experimentally and theoretically demonstrated the superiority of BSW sensors over SPPs sensors [22, 23]. The wavelength sensitivity of 1D-BSW sensors under a Kretschmann configuration is several thousands of nm·RIU−1 [24, 25]. Recent researchers [26] demonstrated fiber-based BSW excitation for RI sensing with a sensitivity of about 650 nm/RIU for p-polarized light and 930 nm/RIU for s-polarized light. Most 1D photonic crystal (1DPC)-based sensors utilize complicated Kretschmann prism-coupled structures to excite BSW. Few researchers have explored grating-coupled-based BSW sensors or other new designs to reduce the complexity of bulk optical components. Vijay et al. [27] did report enhanced sensitivity in a topmost layer grating profile assessed via azimuthal interrogation; the BSW leakage mode is mostly localized inside very narrow grooves which biomolecules do not readily penetrate.

Two-dimensional (2D) grating devices [28,29,30] have attractive potential as miniature RI sensors due to their large sensing areas and relative ease of fabrication. This paper proposes an alternative excitation scheme based on the 2D grating-coupling mechanism. A BSW is realized on the grating side by depositing air-hole arrays on the surface of a Bragg mirror, which supports BSW on both sides. Here, we present one configuration to simply demonstrate the possibility of coupling a BSW on the tip of the grating-coupled Bragg mirror structure, as well as an alternative scheme which demonstrates the influence of available dielectric loss. We compared the optical performance of sensor configurations for BSW excitation at different locations as discussed in detail below.


Case 1: Surface Diffraction-Grating BSW Configuration (DG-BSW)

A schematic diagram of the surface diffraction-grating BSW configuration is shown in Fig. 1. The incident angle θ (angle between the incident beam and Z-axis) and the azimuth angle φ (angle between the negative X-axis and the incident beam projection in the x–y plane) are used to describe the propagation direction of the incident light. In the numerical calculations, we used a five-period DBR (LH)5 where the L dielectrics have RI of 1.46 (SiO2 at the working wavelength of λ0 = 657 nm) and the H layers are made of TiO2 with the RI of 2.57. The RIs of both TiO2 and SiO2 over the range of 0.43 to 0.8 μm are expressed as [27]:

$$ {n}_{SiO_2}={\left(1+\frac{0.6962{\lambda}^2}{\lambda^2-{0.0684}^2}+\frac{0.4080{\lambda}^2}{\lambda^2-{0.1162}^2}+\frac{0.8975{\lambda}^2}{\lambda^2-{9.8962}^2}\right)}^{\frac{1}{2}} $$


$$ {n}_{TiO_2}={\left(5.913+\frac{0.2441{\lambda}^2}{\lambda^2-0.0803}\right)}^{\frac{1}{2}} $$
Fig. 1

Surface diffraction-grating BSW design in (x-y-z) reference system. Structure includes few-period DBR, buffer layer, and 2D grating. Coupling is mediated by a 2D diffraction grating with period Λ = 510 nm, hole radius r = 145 nm, and thickness h = 116 nm. External medium is assumed as air (next = 1)

The imaginary parts of the refractive indices refer to the losses in the dielectric layers. These losses include the intrinsic material absorption and the scattering losses in the incident light (\( {\upgamma}_{{\mathrm{SiO}}_2}=0 \) and \( {\upgamma}_{{\mathrm{TiO}}_2}={10}^{-4} \), in this work). The DBR can be dimensioned accordingly as a quarter-wavelength stack for an incidence angle at the operational wavelength. The thicknesses of the corresponding layers are respectively dL = 100 nm and dH = 70 nm.

To fabricate the surface diffraction-grating BSW sensor, a 116-nm-thick layer of silicon nitride (Si3N4) was deposited on top of the DBR with an air-hole pattern [31, 32] to form the grating layer. A 60 nm-buffer layer which is also made of low refractive index composites (SiO2) was inserted between the Bragg mirror and the sub-wavelength hole-array grating. The grating layer is designed to couple the propagating illuminations to the BSW mode. As described above, grating is essentially a 2D periodic array of structural features made from air holes. In the numerical simulations described below, only the physical dimensions of the grating (period Λ, hole radius r, and thickness h) were adjusted to excite BSW under different illumination conditions and to optimize the reflection profiles.

Under the optimized hole-array grating, when BSW is excited, the reflection from the grating-Bragg configuration forms typical Fano resonant profiles [33] with sharp peaks. The locations of the peaks indicate the RI of the region to be probed. The manufacturing process is simple and compatible with existing MEMS manufacturing technologies, which makes the proposed device mass producible and readily integrated into biochips for multiplexed detection at low cost. We conducted the calculations described here with Diffract MOD integrated in RSoft Photonics Suite, which is based on the rigorous coupled-wave analysis (RCWA) method [34, 35] and contains several advanced algorithms with Fourier harmonics that describe periodic dielectric functions.

Figure 2 shows the simulated electric field distribution for s-polarized light when the surrounding RI is 1. The dashed line in Fig. 2 marks the grating–air interface; z = 0 is the other side surface of the diffraction-grating BSW sensor. As the figure shows, the electric field is strongly enhanced near the interface and the BSW penetrating depth reaches nearly 200 nm in air. The local field intensity is 42 times the maximum incident light intensity at a polar angle of θ = 4.3° and azimuthal angle domain of about φ = 12°.

Fig. 2

Calculated electric field distribution for s-polarized light at resonance where the surface wave is excited on the top surface only. White dotted line represents 2D grating, buffer layer, and DBR layers. Field intensity of BSW mode (yellow region) is concentrated in air holes

Although the proposed structure can, theoretically, provide BSW excitation in the surface diffraction-grating mode, there are effects related to the detection process which merit careful consideration. As shown in Fig. 2, the strong field is concentrated in the small apertures of the hole-array grating. The analyte in the air cannot easily penetrate into the small-size holes, thus gathering above the grating. The decrease in analyte concentration in the holes brings about a small perturbation in the refractive index, which drives down the detection limit and sensitivity of the BSW sensor. The integration of an incident light illumination device and sensing layer also makes on-chip sensor fabrication difficult; further, it is very difficult to estimate the interaction between them. We explored an alternative configuration to overcome these disadvantages while retaining the exponentially decaying electric field distribution.

Case 2: Alternative Guided Grating-Coupled BSW Configuration (GC-BSW)

In the proposed scheme, the sensing region is now moved to the bottom of the grating-coupled BSW sensor, thereby avoiding any detrimental effects related to surface grating structure penetration (Fig. 3). The materials for the DBR, buffer layer, and grating are similar to those described above. Unlike the DG-BSW sensor, the bottom one TiO2 layer thickness was reduced from 70 to 30 nm.

Fig. 3

3D schematic diagram of grating-coupled BSW resonance sensor under azimuthal illuminations (φ) in (x-y-z) reference system including incident angle (θinc), zeroth-order reflection (R0), and 2D grating parameters (Λ, r, h). Sensing region is located at the bottom of the grating-coupled BSW sensor

We placed a bio-solution layer with RI near 1.333 (pure water) adjacent to the outmost high refractive index (TiO2) layer, where the thickness of the region to be probed is 2 μm. We did not need to precisely control the thickness of the sensing layer in this case, because the outer surface of the probed region does not significantly affect BSW mode excitation. Resonance is formed as s-polarized light falls incident on the DBR through the grating at a certain angle, and multiple reflections occur at the bottom defect layer formed by the solution to be tested. The surface defect state structure alters the electromagnetic field distribution on the bottom of the DBR due to surface wave resonance, and multiple reflections in the defect layer form coherent interference. The electromagnetic field is locally enhanced and can fully act on the sample molecules to be tested.

We found that the sensitivity characteristics during dynamic monitoring of the solution to be tested can be improved by the proposed scheme. Similar to SPPs, BSWs are localized at the truncation edge of the 1DPC, at the interface with the external medium. The 2D grating design parameters are the same in the proposed scheme as the previous configuration (DG-BSW): Λ = 510 nm, r = 145 nm, and h = 116 nm. As discussed in detail below, we compared the characteristics of resonant dielectric multi-layer systems DG-BSW and GC-BSW. Our hole-array grating design not only reduces the manufacturing cost, but also provides a relatively fair environment for sensor performance comparison.

Results and Discussion

We designed optimized BSW structures under the two sets of sensing conditions as shown Figs. 1 and 3 with s-polarized light in both cases. Reflectivity curves of these modes as a function of angle of incidence and wavelength are shown in Fig. 4a and b, respectively. DG-BSW and GC-BSW cases have sharp resonance features at their excitation both as a function of angle and wavelength. In the DG-BSW device, when the incident wavelength is around 660 nm, a sharp dip peak appeared at θ = 4.3° by incident angle interrogation. In the GC-BSW device, the resonant angle θ = 7° corresponds to an incident wavelength of 633 nm. We found that although a resonant peak with higher quality factor Q (>103) value can be obtained by optimizing the device parameters, the wavelength sensitivity and angle sensitivity of the BSW sensor reached only about 100 nm/RIU and 280°/RIU under non-azimuthal illuminations. Our 3D RCWA simulations are consistent with the literature [24]. We took into consideration the novel design freedom, azimuthal angle φ, accordingly.

Fig. 4

Bloch surface wave at φ = 0°. Blue and red curves represent BSW reflectance as a function of incident angle (a) and wavelength (b) for DG-BSW and GC-BSW configurations, respectively

The simulated reflection of the GC-BSW sensor designed to work near θ = 7° and φ = 10° is shown in Fig. 5a. BSW coupling occurs in very narrow areas with relatively low reflective intensity (white regions in Fig. 5a). Each polar angle has a corresponding azimuthal angle that satisfies matching conditions to excite the BSW. The BSW mode in the heterostructure decays slowly as polar and azimuthal angles increase, then disappears near θ = 7.6° and φ = 12°. Considering the difficulty of small angle monitoring, we chose a relatively large angle to couple the BSW. The resonance peak is insensitive to polar angle changes but very sensitive to azimuthal angle changes. We calculated the electric field distribution of the sample point (θ = 7°; φ = 9.82°) to recognize the resonance (Fig. 5b). Intensity decays toward the grating/air interface and the field oscillated many times throughout the periodic structure and five peaks formed in the L-H refractive index dielectric interface. The light green dotted line in Fig. 5b represents the refractive index distribution of the GC-BSW sensor in the Z-axis direction. We found that the magnetic field intensity in the bio-solution gradually decays along the Z-direction, as the interaction between light and solution declines with the distance from the truncated layer. The BSW penetration depth reached 2 μm inside the solution, which is tenfold greater than in the DG-BSW configuration.

Fig. 5

a GC-BSW sensor reflection versus azimuthal and polar angles. BSW created by illuminations (λ0 = 633 nm) near θ = 7° and φ = 10°. BSW coupling occurs in very narrow areas (white region) with relatively low reflective intensity. b Electric field (black line) and refractive index distribution (dark green dotted line) inside sensing configurations (case 2 mode). c x-y d x-z plane views of electric field magnitude map, computed at operational wavelength λ0 = 633 nm. White dotted line indicates the locations of the holes in the electric field

Figure 5c and d show electric field magnitude maps in x-y and x-z planes, respectively, computed at the operational wavelength λ0 = 633 nm. The results of Fig. 5b and d are in close accordance. The field distribution at the solution/TiO2 interface largely affects the overall performance of the GC-BSW sensor through the overlap integral between the evanescent field and the spatial distribution of the sensing region’s dielectric constant. We investigated the effects of polar angle on the azimuthal reflection spectra in the GC-BSW configuration by testing polar angles θ of 6.92°, 6.94°, 6.96°, 6.98°, 7°, and 7.02°. To assess high sensitivity, we also determined the full width at half maximum (FWHM) of the resonant dip and the dip peak height. As shown in Fig. 6, typical symmetrical line shapes emerged as the azimuthal angle θ increased. The resonance peak height increased as resonance peak FWHM decreased. At a larger polar angle, the BSW resonance shifted toward a larger azimuthal angle due to the wave vector matching effect.

Fig. 6

Azimuthal reflectance spectra for different incident angles θ. Typical symmetrical line-shapes emerge as azimuthal angle θ increases. The BSW resonances shift to higher azimuthal angles due to wave vector matching effect

Lossless materials (i.e., those with zero values for extinction coefficients κ) are assumed in most numerical simulations [24, 25, 30]. Sinibaldi et al. [36] studied the influence of material losses on the performance of the BSW sensors to find that the extinction coefficient of high index layers κH only slightly affects the resonance characteristics; they introduced an extinction κL = 10−4 to the low index layers calculated via transfer matrix method (TMM). Lossy materials are necessary to observe a dip in the reflectance spectrum [22].

To study the influence of loss, we assessed the azimuthal reflection spectra from DG-BSW and GC-BSW structures (Figs. 1 and 3) with and without considering the loss as shown in Fig. 7. In our case, lossless TiO2 materials can excite the BSW dip peak in the reflection spectrum. Losses in the DBR degrade the BSW line shape obtained in the lossless case. We analyzed the perturbation effect induced by non-zero values for κ on the resonances. In the DG-BSW case, the FWHM of the resonances first decreased and then increased as the extinction coefficient increased from 0 to 10−3, while the resonance depth did the opposite. We achieved the optimal BSW resonance line shape when the extinction coefficient κ reached 10−4. The resonance quickly dropped off as the coefficients further increased (κH = 10−2). In the GC-BSW configuration, the line width increased slowly as κH increased as did the BSW resonance peak value. The resonance dip grew wider as energy losses within the biosensor increased.

Fig. 7

a Resonance line shape variations for DG-BSW configuration and extinction coefficients κH = 0 (lossless), 2 × 10−4, 10−4, 10−3, 10−2. b Variations for GC-BSW configuration. Lossless TiO2 materials excite BSW dip peak in the reflection spectrum. Extinction coefficient values suppress BSW resonance band edge

Our results suggest that lossless TiO2 materials yield optimal BSW resonance. When considering loss, an imaginary part as large as 10−3 can suppress the amplitude of the reflection and the Q of the resonance without affecting the position of the peak. Our simulations also showed that extinction coefficient values play a vital role in determining the optimum compromise between the depth and width (i.e., FWHM) of BSW resonance.

The primary goal of this study was to establish a design schematic for label-free sensing platforms based on a 2D grating to excite BSWs, so we continue to explore sensing locations in order to optimize and enhance its performance as a RI sensor. RI biosensors are generally designed to detect small refractive index modulations caused by variations in biomolecule concentration ratios. We thus consider the azimuthal sensitivity (\( {\mathrm{S}}_{n_{\mathrm{bio}},\varphi } \)) a meaningful observable:

$$ {\mathrm{S}}_{n_{\mathrm{bio}},\varphi }=\frac{\varDelta \varphi}{\varDelta {n}_{\mathrm{bio}}} $$

where Δφ is the change in azimuthal angle and Δnbio is the change in sensing layer refractive index. The reflectivity curves as a function of azimuthal angle for different biomolecule values are shown in Fig. 8. For the DG-BSW configuration, the wavelength (λ0) and incident angle (θ) are fixed at 657 nm and 4.3° respectively (Fig. 8a); for the GC-BSW configuration, λ0 = 633nm and θ = 7° (Fig. 8b). When the refractive index of the biomolecules changes evenly, the BSW resonance peaks blue shift in both cases. That is to say, a small change in the refractive index value (Δnbio = 0.0005) causes the azimuthal angular shift between the resonance peaks to grow larger at small azimuthal angles.

Fig. 8

Reflectivity curves as a function of azimuthal angle for different values of solution. a DG-BSW configuration, where wavelength (λ0) and incident angle (θ) are fixed at 657 nm and 4.3°; b for GC-BSW configuration, λ0 = 633 nm and θ = 7°

We also compared the sensing characteristics of the DG-BSW and GC-BSW configurations to predict sensitivity (black bar) and FWHM (red bar) as shown in Fig. 9 as a function of the surrounding refractive index (SRI). We found that both sensitivity and FWHM monotonically increased as biomolecule variations increased. The sensitivity of the GC-BSW configuration was about twice that of the DG-BSW, while the FWHM of the resonances were narrower in GC-BSW than DG-BSW.

Fig. 9

Sensing characteristics of the DG-BSW (a) and GC-BSW (b) configurations: predicted sensitivity and FWHM as a function of SRI. GC-BSW configuration sensitivity is about twice that of the DG-BSW

Figure of merit (FOM) [25] is another important sensor performance indicator. FOM can be improved in the RI sensor by decreasing FWHM, increasing the spectral sensitivity S [°/RIU], or both, as FOMS/FWHM. The FOM of many optical sensors is constrained by an intrinsic trade-off between spectral sensitivity and FWHM. The azimuthal sensitivity reached 1190°/RIU for the DG-BSW case and 2255°/RIU for the GC-BSW at the maximum extent (Eq. (3)). This implies that the GC-BSW sensor has a closer overlap between the resonant mode and the sensing layer than DG-BSW. The calculations also support the results shown in Figs. 2 and 5b, where the sensing layer of the GC-BSW has a higher light field penetration depth leading to higher sensitivity than DG-BSW.

It is worth noting that the sensitivity of both of the BSW configurations we tested is one order of magnitude higher than that of the conventional prism-based scheme (see Table 1). Unlike any biosensor design based on prism-coupled excitation, there is no strict refractive index limit for the dielectric composite used in DG-BSW or GC-BSW configurations [37,38,39,40,41,42]. By scaling the parameters of 2D grating and DBR properly, the proposed sensor configurations can be effectively realized in any wavelength range.

Table 1 Comparison of layer number, material, and sensitivity of proposed structure with other sensors in literature


In this study, we explored surface diffraction 2D grating configurations and sensing applications. We built a multilayer dielectric heterostructure from subwavelength hole-array grating and distributed Bragg reflection (DBR) with few periods (N = 5) to realize high-sensitivity BSW resonances with low side-bands. A surface DG-BSW configuration and alternative guided GC-BSW schematic were designed based on RCWA methodology. A theoretical sensitivity of 2255°/RIU was achieved with a small polar angle of the illumination (< 10°) and azimuthal angle sweeps around the same values. Angular sensitivity was one order higher than that of sensors based on prism-coupled polar illuminations (generally not larger than 300°/RIU). The optimized GC-BSW sensor showed a particularly large increase in sensitivity (twofold) and narrower BSW resonance compared to the DG-BSW biosensor. Both 2D-grating-coupled sensor platforms tested in this study show low quality factor compared to traditional BSW RI sensors, but they may be enhanced by tuning the period (Λ), hole radius (r), and thickness (h).

The proposed schemes for exciting Bloch surface waves, DG-BSW and GC-BSW, represent new class compact configurations for highly sensitive biosensing and may afford a valuable opportunity to engineer nanoscale “lab-on-chip” technologies in the future.

Availability of Data and Materials

All data generated or analyzed during this study are included in this published article.



1D photonic crystal


Two dimensional


Bloch surface waves


Distributed Bragg reflectors


Diffraction-grating BSW


Figure of merit


Full width at half maximum


Grating-coupled BSW


Quality factor


Rigorous coupled wave analysis


Refractive index




Surface plasmon polaritons


Surface plasmon resonance


Transfer matrix method


  1. 1.

    Inan H, Poyraz M, Inci F, Lifson MA, Baday M, Cunningham BT, Demirci U (2017) Photonic crystals: emerging biosensors and their promise for point-of-care applications. Chem Soc Rev 46(2):366–388

    CAS  Article  Google Scholar 

  2. 2.

    Zhou Y, Scuri G, Wild DS, High AA et al (2017) Probing dark excitons in atomically thin semiconductors via near-field coupling to surface plasmon polaritons. Nat Nanotechnol 12(9):856

    CAS  Article  Google Scholar 

  3. 3.

    Chen J, Zhou J, Zhang Q, Zhang H, Chen M (2018) All-fiber modal interferometer based on a joint-taper-joint fiber structure for refractive index sensing with high sensitivity. IEEE Sensors J 13(7):2780

    Article  Google Scholar 

  4. 4.

    Tazawa H, Kanie T, Katayama M (2007) Fiber-optic coupler based refractive index sensor and its application to biosensing. Appl Phys Lett 91(11):113901

    Article  Google Scholar 

  5. 5.

    Liedberg B, Nylander C, Lunström I (1983) Surface plasmon resonance for gas detection and biosensing. Sensors Actuators 4:299–304

    CAS  Article  Google Scholar 

  6. 6.

    Wang HC, Yu XY, Chueh YL, Malinauskas T, Jarasiunas K, Feng SW (2011) Suppression of surface recombination in surface plasmon coupling with an InGaN/GaN multiple quantum well sample. Opt Express 19(20):18893–18902

    CAS  Article  Google Scholar 

  7. 7.

    Lu LH, Lin YH, Jiang BH, Yeh CH, Kao JC, Chen CP (2017) Microcavity structure provides high-performance (>8.1%) semitransparent and colorful organic photovoltaics. Adv Funct Mater 28(7):1703398

    Article  Google Scholar 

  8. 8.

    Liscidini M, Gerace D, Sanvitto D, Bajoni D (2011) Guided Bloch surface wave polaritons. Appl Phys Lett 98(12):121118

    Article  Google Scholar 

  9. 9.

    Long Y, Shen L, Xu H, Deng H, Li Y (2016) Achieving ultranarrow graphene perfect absorbers by exciting guided-mode resonance of one-dimensional photonic crystals. Sci Rep 6:32312

    CAS  Article  Google Scholar 

  10. 10.

    Kovalevich T et al (2017) Experimental evidence of bloch surface waves on photonic crystals with thin-film linbo3 as a top layer. Photonics Res 5(6):649–653

    CAS  Article  Google Scholar 

  11. 11.

    Rizzo R, Danz N, Michelotti F, Maillart E, Anopchenko A, Wächter C (2014) Optimization of angularly resolved Bloch surface wave biosensors. Opt Express 22(19):23202–23214

    Article  Google Scholar 

  12. 12.

    Rizzo R, Alvaro M, Danz N, Napione L (2018) Bloch surface wave label-free and fluorescence platform for the detection of VEGF biomarker in biological matrices. Sensor Actuat B-Chem 255:2143–2150

    CAS  Article  Google Scholar 

  13. 13.

    Qiao H, Soeriyadi AH, Guan B, Reece PJ, Gooding JJ (2015) The analytical performance of a porous silicon Bloch surface wave biosensors as protease biosensor. Sensor Actuat B-Chem 211:469–475

    CAS  Article  Google Scholar 

  14. 14.

    Yang N, Chen C, Li T et al (2019) Portable rice disease spores capture and detection method using diffraction fingerprints on microfluidic chip. Micromachines 10(5):289

    Article  Google Scholar 

  15. 15.

    Yang N, Wang P, Xue C et al (2018) A portable detection method for organophosphorus and carbamates pesticide residues based on multilayer paper chip. J Food Process Eng 41(8):e12867

    Article  Google Scholar 

  16. 16.

    Nishi H, Hiroya S, Tatsuma T (2015) Potential-scanning localized surface plasmon resonance sensor. ACS Nano 9(6):6214–6221

    CAS  Article  Google Scholar 

  17. 17.

    Masson JF (2017) Surface plasmon resonance clinical biosensors for medical diagnostics. ACS sensors 2(1):16–30

    CAS  Article  Google Scholar 

  18. 18.

    Michel D, Xiao F, Alameh K (2017) A compact, flexible fiber-optic surface plasmon resonance sensor with changeable sensor chips. Sensor Actuat B-Chem 246:258–261

    CAS  Article  Google Scholar 

  19. 19.

    Yeh P, Yariv A, Cho AY (1978) Optical surface waves in periodic layered media. Appl Phys Lett 32:104–105

    CAS  Article  Google Scholar 

  20. 20.

    Wu IC, Weng YH, Lu MY et al (2017) Nano-structure ZnO/Cu2O photoelectrochemical and self-powered biosensor for esophageal cancer cell detection. Opt Express 25(7):7689–7706

    CAS  Article  Google Scholar 

  21. 21.

    Wang HC, Nguyen NV, Lin RY, Jen CP (2017) Characterizing esophageal cancerous cells at different stages using the dielectrophoretic impedance measurement method in a microchip. Sensors 17(5):1053

    Article  Google Scholar 

  22. 22.

    Sinibaldi A, Danz N, Descrovi E et al (2012) Direct comparison of the performance of Bloch surface wave and surface plasmon polariton sensors. Sensor Actuat B-Chem 174:292–298

    CAS  Article  Google Scholar 

  23. 23.

    Li Y, Yang T, Pang Z et al (2014) Phase-sensitive Bloch surface wave sensor based on variable angle spectroscopic ellipsometry. Opt Express 22(18):21403–21410

    Article  Google Scholar 

  24. 24.

    Kang XB, Wen LW, Wang ZG (2017) Design of guided Bloch surface wave resonance bio-sensors with high sensitivity. Opt Commun 383:531–536

    CAS  Article  Google Scholar 

  25. 25.

    Lereu AL, Zerrad M, Passian A, Amra C (2017) Surface plasmons and Bloch surface waves: towards optimized ultra-sensitive optical sensors. Appl Phys Lett 111(1):011107

    Article  Google Scholar 

  26. 26.

    Tu T, Pang F, Zhu S et al (2017) Excitation of Bloch surface wave on tapered fiber coated with one-dimensional photonic crystal for refractive index sensing. Opt Express 25(8):9019–9027

    CAS  Article  Google Scholar 

  27. 27.

    Koju V, Robertson WM (2017) Leaky Bloch-like surface waves in the radiation-continuum for sensitivity enhanced biosensors via azimuthal interrogation. Sci Rep 7:3233

    Article  Google Scholar 

  28. 28.

    Sreekanth KV, Alapan Y, ElKabbash M et al (2016) Extreme sensitivity biosensing platform based on hyperbolic metamaterials. Nat Mater 15(6):621

    CAS  Article  Google Scholar 

  29. 29.

    Sørensen KT, Ingvorsen CB, Nielsen LH, Kristensen A (2018) Effects of water-absorption and thermal drift on a polymeric photonic crystal slab sensor. Opt Express 26(5):5416–5422

    Article  Google Scholar 

  30. 30.

    Ge D, Shi J, Rezk A et al (2019) Optical Fano resonance sensing of bilayer asymmetric photonic crystal slabs as biosensors. Appl Opt 58:3187–3192

    CAS  Article  Google Scholar 

  31. 31.

    Wang S, Liu Y, Zhao D et al (2017) Optofluidic Fano resonance photonic crystal refractometric sensors. Appl Phys Lett 110(9):091105

    Article  Google Scholar 

  32. 32.

    Ge D, Lu L, Zhang J et al (2017) Electrochemical fabrication of silicon-based micro-nano-hybrid porous arrays for hybrid-lattice photonic crystal. ECS J Solid State Sci Technol 6:P893–P897

    CAS  Article  Google Scholar 

  33. 33.

    Fan S, Joannopoulos JD (2002) Analysis of guided resonances in photonic crystal slabs. Phys Rev B Condens Matter 65(23):235112

    Article  Google Scholar 

  34. 34.

    Moharam MG, Gaylord TK (1981) Rigorous coupled-wave analysis of planar-grating diffraction. J Opt Soc Am 71(7):811–818

    Article  Google Scholar 

  35. 35.

    Moharam MG, Grann EB, Pommet DA, Gaylord TK (1995) Formulation for stable and efficient implementation of the rigorous coupled-wave analysis of binary gratings. J Opt Soc Am A 12(5):1068–1076

    Article  Google Scholar 

  36. 36.

    Sinibaldi A, Rizzo R, Figliozzi G et al (2013) A full ellipsometric approach to optical sensing with Bloch surface waves on photonic crystals. Opt Express 21(20):23331–23344

    CAS  Article  Google Scholar 

  37. 37.

    Khan MU, Corbett B (2016) Bloch surface wave structures for high sensitivity detection and compact waveguiding. Sci Technol Adv Mat 17(1):398–409

    CAS  Article  Google Scholar 

  38. 38.

    Rodriguez GA, Lonai JD, Mernaugh RL et al (2014) Porous silicon Bloch surface and sub-surface wave structure for simultaneous detection of small and large molecules. Nanoscale Res Lett 9(1):383

    Article  Google Scholar 

  39. 39.

    Rodriguez GA, Ryckman JD, Jiao Y et al (2014) A size selective porous silicon grating-coupled Bloch surface and sub-surface wave biosensor. Biosens Bioelectron 53:486–493

    CAS  Article  Google Scholar 

  40. 40.

    Wu Y, Wu P, Chao Y et al (2017) Gas-exfoliated porous monolayer boron nitride for enhanced aerobic oxidative desulfurization performance. Nanotechnology 29(2):025604

    Article  Google Scholar 

  41. 41.

    Ge D, Shi J, Wei J et al (2019) Optical sensing analysis of bilayer porous silicon nanostructure. J Phys Chem Solids 130:217–221

    CAS  Article  Google Scholar 

  42. 42.

    Shi J, Rezk A, Ma C et al (2019) Excitation of Bloch surface wave using silver nanoparticles for sensitivity enhanced biosensor. Mater Res Express 6(9):095042

    Article  Google Scholar 

Download references


This work was supported by the National Natural Science Foundation of China (NSFC) (11404146); Natural Science Foundation of Jiangsu Province, China (BK20180098); China Post-doctoral Science Foundation (2018 M630543); and Open Research Fund of National Laboratory of Solid State Microstructures (M32045).

Author information




JS and LZ carried out the simulation and analysis. AR and CM created the figures. PY and SZ participated in the discussion and gave useful suggestions. The manuscript was composed by DG and JS. All authors read and approved the final manuscript.

Corresponding authors

Correspondence to Daohan Ge or Liqiang Zhang.

Ethics declarations

Competing Interests

The authors declare that they have no competing interests.

Additional information

Publisher’s Note

Springer Nature remains neutral with regard to jurisdictional claims in published maps and institutional affiliations.

Rights and permissions

Open Access This article is distributed under the terms of the Creative Commons Attribution 4.0 International License (, which permits unrestricted use, distribution, and reproduction in any medium, provided you give appropriate credit to the original author(s) and the source, provide a link to the Creative Commons license, and indicate if changes were made.

Reprints and Permissions

About this article

Verify currency and authenticity via CrossMark

Cite this article

Ge, D., Shi, J., Rezk, A. et al. Two-Dimensional Hole-Array Grating-Coupling-Based Excitation of Bloch Surface Waves for Highly Sensitive Biosensing. Nanoscale Res Lett 14, 319 (2019).

Download citation


  • 2D grating
  • Bloch surface wave
  • Sensitivity
  • Refractive index sensors