Dual-polarized highly sensitive plasmonic sensor in the visible to near-IR spectrum

We propose and numerically characterize the optical characteristics of a novel photonic crystal fiber (PCF) based surface plasmon resonance (SPR) sensor in the visible to near infrared (500–2000 nm) region for refractive index (RI) sensing. The finite element method (FEM) is used to design and study the influence of different geometric parameters on the sensing performance of the sensor. The chemically stable plasmonic material gold (Au) is used to produce excitation between the core and plasmonic mode. On a pure silica (SiO2) substrate, a rectangular structured core is used to facilitate the coupling strength between the core and the surface plasmon polariton (SPP) mode and thus improves the sensing performance. By tuning the geometric parameters, simulation results show a maximum wavelength sensitivity of 58000 nm/RIU (Refractive Index Unit) for the x polarization and 62000 nm/RIU for the y polarization for analyte refractive indices ranging from 1.33 to 1.43. Moreover, we characterize the amplitude sensitivity of the sensor that shows a maximum sensitivity of 1415 RIU−1 and 1293 RIU−1 for the x and y polarizations, respectively. To our knowledge, this is the highest sensitivity for an SPR in published literature, and facilitates future development of sensors for accurate and precise analyte measurement. The sensor also attains a maximum figure of merit (FOM) of 1140 and fine RI resolution of 1.6 × 10−6. Owing to strong coupling strength, high sensitivity, high FOM and improved sensing resolution, the proposed sensor is suited for real-time, inexpensive and accurate detection of biomedical and biological analytes, biomolecules, and organic chemicals. © 2018 Optical Society of America under the terms of the OSA Open Access Publishing Agreement


Introduction
In the last few decades, surface plasmon resonance (SPR) sensing technology has reached a unique place because of its ability to achieve high sensitivity and reliability [1]. Note that SPR is an optical phenomenon that can be defined as the collective oscillation of free electrons on the interface between the metal and dielectric. Resonance occurs when the wavelength of photons of the incoming electromagnetic wave matches with the wavelength of surface electrons. At resonance condition, a sharp loss peak is obtained for a particular analyte of RI and an unknown analyte with different RI can be detected by observing the variation of loss peak and corresponding resonance wavelength. A tiny change in environmental RI potentially shifts the resonance wavelengths, and offers potential application in bio-sensing for label-free and real-time detection of the kinetics of various biological processes [2]. The other significant application areas of SPR sensors range from medical diagnostics, medical testing, bio-molecular analyte detection, antigen-antibody interactions, environmental monitoring for security and food safety [3][4][5]. Moreover, SPR technology is considered advantageous because of its effectiveness However, a maximum wavelength and amplitude sensitivity of 46000 nm/RIU and 1086 RIU −1 was obtained with an analyte RI of 1.33 to 1.43 [29]. Although cleaning a D-shaped structure is convenient for refilling with analyte, the standard polishing and etching of particular parts are challenging in practice [33,34].
Considering the limitations faced by the internal sensing approach as well as D-shaped structure of the external sensing approach, PCFs with a different external sensing mechanism were reported where the analyte channel is in contact with the outer surface of the PCF [10,[35][36][37][38][39]. Among the PCFs proposed with this external sensing approach, Liu et al. recently obtained a maximum wavelength sensitivity of 15180 nm/RIU within the analyte RI of 1.40 to 1.43 [39]. Therefore, the literature discussed above indicates that there is sufficient scope for new SPR sensor designs with improved sensing performance.
In this manuscript, utilizing an external sensing approach we propose a novel gold coated PCF-SPR sensor to operate in the visible to near-infrared region. Note that at near-infrared the penetration depth of the evanescent field is high resulting in improved detection of analytes, and low-cost laser sources are commercially available [40]. We introduce a rectangular shaped core structure that facilitates coupling, which further improves the sensing performance. The aim is to obtain high detection accuracy in a sensor that can be readily fabricated. For ease of fabrication and practical utilization of the sensor, the metal coating is applied to the outer surface of the fiber, with the plasmonic surface in direct contact with the analyte. Various geometric parameters such as pitch distance, air hole diameter, core geometry, analyte channel thickness, metallic channel thickness and PML thickness are optimized for obtaining the desired performance.

Design and theoretical modelling of the proposed PCF-SPR sensor
The modelling and performance evaluation of the proposed PCF-SPR sensor are carried out using commercially available finite element method (FEM) based software COMSOL v5.3. The schematic of the proposed sensor is shown in Fig. 1 (a). Physics-controlled mesh sequence with extremely fine element size is used to achieve maximum accuracy in simulation. In a silica (SiO 2 ) substrate, a circular air hole based circular shaped cladding is proposed.
Different diameters of air holes (d, d 1 and d 2 ) are used to shape the cladding that has significant effect on confinement loss and light propagation through fiber that is discussed in the later section of this manuscript. Here, air holes with diameter d are used to couple light from core mode to interact with the plasmonic mode so that a strong interaction between core and plasmonic mode can be created. The air holes with diameter d 1 confine light from the core mode, to the plasmonic mode aside from the outer holes. In this way the power density in the core mode is increased to interact strongly throgh the specified area of plasmonic mode. In addition, the air holes with diameter d 2 are used to reduce the confinement loss. A rectangular air hole is used at the center of the core to create asymmetry between the polarization modes that in turn helps improving the sensing performance [41]. Addition of rectangular air hole in the core help the core power to strongly couple with the surface that also help creating birefringence effect on the sensor. Moreover, we use four channels of light penetration from the core mode to the plasmonic mode to improve the performance of the sensor. Note that an artificial boundary condition named perfectly matched layer (PML) is added at the outer surface of the computational region that potentially absorbs radiation energy. We optimize the air hole diameters (d, d 1 and d 2 ), rectangle width (W) and height (H), pitch distances (Λ, Λ 1 and Λ 2 ), gold (t g ), analyte (t a ) and PML (t p ) thickness to determine the optimal design conditions. After careful investigation we choose H = 0.5 µm, W = 0.15 µm, Λ = 1.8 µm, Λ 1 = 1.6 µm, Λ 2 = 1.24 µm, d = 1.35 µm, d 1 = 1.20 µm, d 2 = 0.18 µm, t g = 30 nm, t a = 0.9 µm, and t p = 1.0 µm as optimal. Optimization of these parameters is briefly discussed in Section 3. In the designed sensor, the analyte is in contact with the outer surface that can be cleaned for reuse with different analytes-this removes the difficulties with internal sensing as well as external sensing with a D-shaped structure that needs careful surface polishing [29,32].
The material dispersion of pure silica can be calculated using the Sellmeier Eq. [31,43], where n represents the RI of silica and λ stands for the wavelength of light. Note that, Eq. (1) is valid for the wavelength region of 0.37 to 2.2 µm [31,43]. The material dispersion of gold can be determined from the Drude-Lorentz model [42,44], where ε ∞ = 5.9673 is the permittivity of gold, ∆ ε = 1.09 is the weighting vector, ω is the angular frequency of the guided light, ω D and γ D are defined as the plasma frequency and damping frequency, where ω D /2π = 2113.6 THz, and γ D /2π = 15.92 THz. Moreover, Ω L and Γ L indicate the frequency and spectral width of the Lorentz oscillator where Ω L /2π = 650.07 THz and Γ L /2π = 104.86 THz. Confinement loss of the proposed sensor can be calculated by using the imaginary part of the complex RI by using both the following Eq. [29], where, α loss stands for the confinement loss, λ specifies the operating wavelength in micron scale, and Im(n eff ) represents the imaginary part of the complex RI. Note that the performance evaluation of the proposed sensor is carried out using both wavelength interrogation (WI) and amplitude interrogation (AI) method. According to WI method the wavelength sensitivity can be calculated according to the following Eq. [32], where, ∆λ peak and ∆n a denotes the shift in resonance peaks and analyte RI respectively.
It can be mentioned that the AI method is less complex since in this method the output beam is analyzed at a particular wavelength where spectral manipulation is not needed [45]. Therefore, AI method only requires a power meter and however, AI is very sensitive to disturbances. Usually ratiometric approaches are used, where the sensitive intensity is compared to the intensity of a reference peak which is not sensitive to the parameter to be measured and thus any fluctuation in laser power, coupling, etc is removed via normalising to the reference peak intensity. If the input power launched into the fiber is P 0 , the detected power at the output can be found by the following expression where, α(λ, n a ) is the attenuation constant and can be defined by Eq. (3), L indicate the length of the sensor that can be defined by .
The amplitude sensitivity of the sensor can be calculated according to the following Eq. [45], δn a (7) where, the difference between two loss spectra due to a small change of analyte RI is denoted by δα(λ, n a ), and δn a indicates the change in analyte RI. Preserving the polarization state is also important in consideration of sensing applications; eliminating the polarization mode dispersion (PMD), as well as stabilizing the operation of optical devices. Birefringence determines the polarization states of a fiber that is defined as the RI difference between the polarization modes. It can be calculated by the following Eq. [46,47], here, B indicates the birefringence, n x represents the effective mode index in the x-polarization and n y represents the effective mode index in the y-polarization. Sensor resolution is also an important parameter that determines the degree of detection with analyte RI variation. The resolution of a sensor can be determined by the following Eq. [48], R = ∆n a ∆λ min ∆λ peak (9) where, R represents the sensor resolution, ∆n a represents the variation of analyte RI, ∆λ min defines the minimum wavelength resolution, and ∆λ peak determines the difference in resonance peak shift. The fabrication of the proposed sensor is straightforward. The differently sized circular shaped air holes can be realized using the standard stack-and-draw method [49,50]. In 2014, Mahdiraji et al. [49] and Knight et al. [50] utilized the stack-and-draw method to make different circular shaped air holes. Moreover, the rectangular shaped air hole can be fabricated using an extrusion technique [51,52] and 3D printing technology [53]. Note that, Atakaramians et al. [51,52] made the rectangular shaped air holes utilizing the extrusion technique. There are several methods such as chemical vapor deposition (CVD), high-pressure microfluidic chemical deposition and wheel polishing for obtaining a thin gold layer at the outer surface of the sensor [18,30,[54][55][56][57]. Therefore, the proposed sensor is manufacturable with available fabrication technologies.
A general set-up for practical realization of the sensor is shown in Fig. 1(b). A wide-band or super-continuum light source can be used to launch light into the single mode fiber (SMF). A splicing technique can be used then to couple the SMF with the proposed sensor. An analyte flow channel at the outer layer facilitates the IN and OUT of liquid analyte. The IN and OUT of analytes can be maintained by using a pump. Note that due to the interaction of ligand and analyte, the effective index of the SPP mode is expected to be changed resulting in red or blue shift of the signal. The optical spectrum analyzer can be used to measure the transmitted light through another SMF. Finally the computer can be used to observe and analyze the output spectrum.

Investigation of sensor performance by optimizing different optical parameters
The evanescent field produced by the light propagating through the core is the key phenomenon of a PCF-SPR sensor. The evanescent field excite the electrons of the metal surface that result in a surface plasmon wave. As the proposed sensor experiences birefringence due to its asymmetrical structure, we investigate the sensing performance for both polarizations. As an initial step we characterize the evanescent field distribution that indicates strong coupling between the core and SPP mode for both polarization modes as shown in Fig. 1(c)-(j). At resonance wavelength Fig. 1(c)-(j) shows the field distribution for n a = 1.33 and n a = 1.42 respectively which shows that for n a = 1.42 the mode fields are more strongly coupled than n a = 1.33. These results strong detection of analyte with RI higher than n a = 1.33. The dispersion profile for fundamental core mode, plasmonic mode and confinement loss as a function of wavelength for both x and y polarization is shown in Fig. 2 (a-b). It indicates that at the RI matching point of core mode and SPP mode a sharp loss peak is obtained, and sharp loss peak is suitable for efficient and easy detection of analytes [29]. It can be seen from Fig. 2 (a-b) that, for an analyte RI of n a = 1.42 and x polarization the resonance occurred at a wavelength of 1.07 µm whereas for the y polarization the resonance point shifted to 1.10 µm. This clearly indicates a significant amount of birefringence in this PCF design resulting in strong coupling to one of the two possible orientations. The polarization property of a fiber sensor improves the sensing performance [29,47].
The characteristics of confinement loss for both the polarizations at an analyte RI variation from 1.33 to 1.43 is shown in Fig. 2 (c-d). Note that, performance measurement of the sensor is carried out using the confinement loss characteristics of different analytes. Figure 2 (c-d) indicate that increase of analyte RI shifts the resonance peak towards longer wavelengths. Note that with a tiny change of analyte RI, the RI of plasmonic mode also changes resulting in a changed phase matching point. During the performance analysis we choose RI from 1.33 to 1.43. This is because the RI of biochemical interactions goes from 1.33 to 1.35 however the range 1.33 to 1.43 is considered based on practical bio-chemical and chemical sensing [60,61]. It is observed that the resonance peak shift increases with the increase of analyte RI resulting in high sensitivity for larger RI. Note that the proposed sensor shows similar loss characteristics to previously reported [32] highly sensitive sensors. Moreover, from Fig. 2 (c-d) we can see that a maximum resonance wavelength shift of 580 nm and 620 nm is obtained between the analyte RI of 1.42 and 1.43 for the x and y polarization mode respectively. Therefore, a maximum wavelength sensitivity of 58000 nm/RIU and 62000 nm/RIU is obtained at 1.42. To our knowledge, this is the highest wavelength sensitivity reported by a PCF-SPR sensor.
The performance evaluation of the sensor is also carried out using the amplitude interrogation method that calculates amplitude sensitivity. The obtained amplitude sensitivity at both x and y polarization mode is shown in Fig. 2 (e-f). It can be seen that x polarization shows better amplitude sensitivity than y polarization as sharper loss peak is obtained at x than y polarization. The maximum amplitude sensitivity obtained for the x polarization is 1415 RIU −1 whereas for the y polarization the sensitivity is 1293 RIU −1 .
Note that, to evaluate the overall performance of a sensor, the FOM is defined as the ratio of sensitivity to full width at half minima (FWHM) [32,58,59]. In general, to realize a high performance sensor the FOM should be as high as possible that can be obtained when the sensitivity increases and FWHM decreases. The obtained FOM for different analyte is shown in Table 3. We can see that, a maximum FOM of 1140 and 958 is obtained for the x and y polarization respectively that also an indication of improved performance of the proposed sensor over the prior reported [6,10,[17][18][19][20][21][22][23][24][25][26][29][30][31][32][33][34][35][36][37][38][39] sensors.
For different variation of analyte RI Table 3 shows the characteristics comparison of the proposed sensor for both x and y polarization at optimal design conditions. It indicates that maximum amplitude sensitivity of 1415 RIU −1 is obtained at x polarization mode, this is due to the sharper loss characteristics of x polarization than y polarization (see Fig. 2 (c-d)). Moreover, we can see that the maximum amplitude sensitivity is obtained at an analyte RI of 1.39 and it decreases with further increase or decrease of RI from 1.39 (see Fig. 2 (e-f)). This is because of the sharper loss peak obtained between the RI of 1.39 to 1.40 whereas the loss peak broadens for other RI of analytes.

Effect of different core structures on the sensing performance
The effect of different core structures on the sensing performance of the proposed sensor is investigated. We used different core structure such as rectangular, circular and solid core and analyzed their performance to choose the best one. It is worthwhile to note that there is no particular reason but we randomly choose the RI 1.41 and 1.42 as a reference to observe the characteristics of the sensor at different geometric parameter variations. Thus, by tuning different geometric parameters, further investigation of the sensor is done using analyte RI of 1.41 and 1.42 as reference.

Performance with solid core
The performance of the sensor with solid core is investigated, with the loss and sensitivity shown in Fig. 3 (a). It shows that solid core experience negligible confinement loss with amplitude and wavelength sensitivity of 886 RIU −1 and 10000 nm/RIU respectively for an analyte RI of n a = 1.41.

Performance with circular shaped air hole in the core
The effect of circular shaped air hole in the core on the sensing performance of the PCF-SPR sensor is also investigated, as shown in Fig. 3 (b). It indicates that use of circular shaped air hole in the core instead of the solid core increases the confinement loss however that also comes with a lower amplitude sensitivity (660 RIU −1 ) with same wavelength sensitivity.

Performance with rectangular shaped air hole in the core
The performance analysis of the core with rectangular shaped air hole is carried out by varying the height (H) and width (W). For different values of (H) and (W) the characteristics are shown in Fig. 3 (c-h). From Fig. 3 (c-d) it can be observed that increasing the rectangular height increases the confinement loss by increasing coupling from the core mode to the SPP mode. However, that also reduces the amplitude sensitivity that can be observed from Fig. 3 (e). We can see that as H increases the loss peak also broadens causing a reduction in amplitude sensitivity. Therefore, we cannot consider H = 0.7 µm as an optimum height of the rectangular core. Moreover, for H = 0.3 µm we can see that the confinement loss decreases and amplitude sensitivity increases significantly as compared to H = 0.7 µm. However this also broadens the loss peak and reduces the birefringence therefore we also cannot consider H = 0.3 µm as optimum. Note that the broadened characteristic of the loss peak is not suitable for efficient and accurate detection as it decreases the signal to noise ratio that may give rise to a false positive response [29]. For H = 0.5 µm it can be observed that a sharp loss peak associated with a highest amplitude sensitivity is obtained for both of the polarization modes. Moreover the obtained wavelength sensitivity at H = 0.5 µm is higher (15000 nm/RIU) than H = 0.3 µm (14000 nm/RIU). Thus considering all of the above facts we choose H = 0.5 µm as optimum height of the rectangular shaped air hole in the core.
In order to optimize the width (W) of the rectangular core we varied W to observed the confinement loss and sensitivity performances that illustrated in Fig. 3 (f-h). With W = 0.10 µm, a minimum loss and high amplitude sensitivity is observed, however that also results in a broadened loss peak. We can observe a comparatively sharper loss peak for W = 0.15 µm and W = 0.20 µm, however the larger width also results in a lower sensitivity. Thus, considering the amplitude sensitivity and confinement loss we choose W = 0.15 µm as the optimum width of the rectangular core.
The electric field distribution due to the solid core and core with circular shaped air hole is shown in Fig. 3 (i-p), it indicates that at resonance wavelength the coupling of core mode and SPP mode is weaker than that obtained for rectangular core as shown in Fig. 1 (c-j). Therefore, we obtain better sensing performance by using rectangular shaped air hole in the core than using solid and circular shaped air hole. Therefore, observing the obtained characteristics and analyzing the sensing performances we decide to consider the rectangular shaped structure in the core of the proposed sensor. The birefringence effect of the sensor using rectangular, circular and solid core is shown and observed from Fig. 4 (a). It indicates that the birefringence effect of a rectangular shaped core is significant as it can create more asymmetry between the polarization modes whereas the circular and solid cores are able to create almost zero birefringence as there is no asymmetry in the structure. We can see from Fig. 4 (a) that the birefringence for the rectangular core increases with wavelength. This is because, at higher wavelength the index difference between the polarization modes increases and that results high birefringence. As we mentioned earlier, the birefringence effect of a fiber makes the coupling stronger either in x polarization or y polarization that increases the sensitivity as well as the detection accuracy [38]. Note that, this is another reason of choosing the rectangular structure as the core of the proposed sensor. Fig. 4. Birefringence with different shaped core air hole (a), confinement loss (b-c) and amplitude sensitivity (d) at optimal d, d 1 , d 2 and ±2% variation from the optimal diameters for n a = 1.41, confinement loss (e-f) and amplitude sensitivity (g) at optimal Λ, Λ 1 , Λ 2 and ±2% variation from the optimal for n a = 1.41, confinement loss (h-i) and amplitude sensitivity (j) at different variation of gold thickness, and confinement loss (k-l) at different analyte thickness variation.

Effect of cladding on the sensing performance
With rectangular air hole in the core, the effect of cladding on the sensing performance including air hole diameters (d, d 1 and d 2 ) and pitch distances (Λ, Λ 1 , and Λ 2 ) are investigated. This is also done to optimize the air hole diameters and pitch distances. In order to choose optimum diameters of cladding air holes we varied d, d 1 and d 2 and observed the sensing performance that is shown through Fig. 4 (b-d). It indicates that changing d, d 1 and d 2 from its optimum diameter changes the loss characteristics, however the variation is not very significant. However, such variation affects the amplitude sensitivity, as shown in Fig. 4 (d). It can be seen that variation of air hole diameters from its optimum causes broadening of the loss peak and reduces amplitude sensitivity. It can be seen that a sharp loss peak and maximum sensitivity is obtained at d = 1.35 µm, d 1 = 1.20 µm, d 2 = 0.18 µm and thus we choose those values of d, d 1 and d 2 as optimum cladding air hole diameter.

Effect of pitch distances Λ, Λ 1 , and Λ 2
The effect of pitch distances of the air holes is also investigated. Fig. 4 (e-g) shows the characteristics of the proposed sensor with different pitch variation at both x and y polarizations. From Fig. 4 (e-f) we can see that changing the pitch distances does not significantly change the confinement loss. However, comparing the loss characteristics with different pitch values we found sharper loss peak at Λ = 1.8 µm, Λ 1 = 1.6 µm, Λ 2 = 1.24 µm. As such, due to sharper loss peak, a maximum amplitude sensitivity is obtained at those values of pitch distance. Note that by varying the pitch distances, the sensor shows no significant change in wavelength sensitivity, however significant change in amplitude sensitivity is found as shown in Fig. 4 (g).

Effect of gold thickness on sensing performance
The thickness of the gold layer plays an important role on the sensing performance. Gold thickness also significantly affects the resonance wavelength shift. Thus the effect of gold thickness variation on the overall sensing performance is investigated. It can be seen from Fig.  4 (h-i) that as the gold thickness increases the resonance peak shifts largely towards the longer wavelengths. Moreover, it can be seen that a thicker Au layer broadens the loss peak and increases the signal to noise ratio (SNR) of the sensor.
We can see that for t g = 40 nm the loss is larger, with near zero amplitude sensitivity (Fig. 4 (j)), therefore we rule out t g = 40 nm as optimum. It can also be observed that, at t g = 20 nm the loss is lower and the obtained amplitude sensitivity is higher than t g = 30 nm. However, the obtained wavelength sensitivity at t g = 30 nm is higher (15000 nm/RIU for x-pol and 15000 nm/RIU for y-pol for n a = 1.41) than the obtained sensitivity at t g = 20 nm (11000 nm/RIU for x-pol and 13000 nm/RIU for y-pol of n a = 1.41). The sensitivity reduction for thinner gold layer is due to the skin depth limitation of the surface plasmons [3,4,31]. Moreover, making a 30 nm gold layer is easier than a 20 nm layer. Thus considering all of the above facts we choose t g = 30 nm as an optimal gold thickness for the proposed sensor.
We can see from Fig. 4 (k-l) and Fig. 5 (a) that analyte thickness has significant impact on the sensor performance. It can be observed that when the channel thickness decreases to t a = 0.81 µm from the optimum point (t a = 0.9 µm) the amplitude as well as wavelength sensitivity decreases (13000 nm/RIU for x-pol and 14000 nm/RIU for y-pol of n a = 1.41). The similar thing happened when we increased the channel thickness to t a = 0.99 µm. Therefore, considering the amplitude sensitivity, wavelength sensitivity and loss peak broadening we consider t a = 0.90 µm as optimum analyte thickness.

Effect of PML thickness on sensing performance
Finally, we optimize the thickness of the perfectly matched layer and the characteristics are observed from Fig. 5 (b-d). The confinement loss characteristics as shown in Fig. 5(b-c) indicate that PML has very little impact on the confinement loss of the sensor. For different thickness of PML Fig. 5(d) indicate that when the PML thickness reduces to t p = 0.80 µm than the optimum (t p = 1.0 µm) the amplitude sensitivity greatly decreases. However, PML thickness greater than 1.0 µm produced similar sensing performance as that obtained with t p = 1.0 µm. Therefore, we could choose t p = 1.20 µm or more however that also increases the overall size of the sensor. Thus, considering the sensing performance and size of the sensor we choose t p = 1.0 µm as optimal PML thickness.

Sensor Length and Resolution Property
It is also important to investigate the length of the sensor that can be achieved using Eq. (5 (e)). As can be observed from Eq. (5 (e)) that, the length of a sensor is totally dependent on its attenuation constant. For different RI, the length of the sensor is shown in Fig. 5 (e) which indicate that the attenuation constant (α) increases with the increase of RI resulting reduction in sensor length. It can be seen that a sensor having length of centimetres to few millimetres can be used to detect analytes with different RI. The resolution of a sensor is an important parameter by which the detection limit of the sensor can be investigated. By considering ∆λ min = 0.1 nm, a maximum resolution of 1.72 × 10 −6 and 1.61 × 10 −6 is obtained for the x and y polarization, respectively. To our knowledge this is the highest resolution obtained as compared to prior reported PCF based plasmonic sensors. Note that, the resolution of the proposed sensor indicates that the sensor has the capability to detect a tiny change of RI of the order of 10 −6 . Therefore, the proposed sensor can effectively be used to detect the tiny change of analyte RI.
A performance analysis of the proposed PCF-SPR sensor with the prior sensors is carried out in Table 3.3. Based on the performance analysis of wavelength sensitivity, amplitude sensitivity, sensor resolution and birefringence it can be seen that the proposed sensor shows improved performance over the prior sensors presented in the literature. Moreover, due to practical sensing approach, the proposed sensor increases its potential for further real time measurements of analytes.

Conclusions
A novel PCF based SPR sensor has been designed and characterized for optical detection of biological, biochemical and biomedical analytes. Detailed numerical simulation and extensive analysis of the sensor shows a maximum wavelength sensitivity of 58000 nm/RIU for x polarization and 62000 nm/RIU for y polarization, maximum amplitude sensitivity of 1415 RIU −1 for x polarization and 1293 RIU −1 for y polarization respectively within the analyte RI of 1.33 to 1.43. Moreover, the sensor can achieve a maximum birefringence of 1.2 × 10 −3 that facilitates the fiber to be operated in a dual polarized mode and improves the sensing performance. The sensor also shows a maximum resolution of 1.72 × 10 −6 and 1.6 × 10 −6 for the x and y polarization respectively. Moreover, the sensor achieves a maximum FOM of 1140 for the x polarization and 958 for the y polarization that validates the performance improvement of it. To our knowledge the obtained sensitivity and sensor resolution is better than any prior reported PCF-SPR sensors. The fabrication of the sensor is straightforward with existing technologies. The practical utilization is simple as it uses an external sensing approach. With such remarkable sensing properties the proposed sensor shows great potential in the field of biomedicine, chemistry and for accurate and precise detection of other biological and biomedical agents.