Photonic Crystal Fibers (PCFs) have special structures and offer a number of novel design options, such as very large or very small mode areas, high numerical aperture, guidance of light in air, and novel dispersion properties.PCFs have become an attractive field for the researchers and they are trying to work on these to get their properties applied in dispersion related applications, sensing applications and much more.PCFs sensors are widely used in bio-medical applications. The sensitivity and performance of sensors are enhanced due to novel applications of PCFs.This paper outlines a novel design for a generalized biomedical sensor by collaborating PCF and electro-optic effect of Lithium Niobate (LiNbO_3) based Mach-Zehnder interferometer (MZI) structure

Albertazzi Gonçalves, Armando

Amphawan, Angela

Bisht, Akanksha

Bisht, Ashish

Kumar, Santosh

Lehmann, Peter

Osten, Wolfgang

Singh, Gurdeep

UUM Repository

   Design of Photonics Crystal Fiber Sensors for Bio-medical Applications  Santosh Kumar*a, Akanksha Bishta, Ashish Bishta, Gurdeep Singha, Angela Amphawanb aDepartment of Electronics & Comm. Engineering, DIT University, Dehradun-248009, India; bFulbright Research Fellow, Massachusetts Institute of Technology, 02139 Cambridge, Massachusetts, USA; bInterNetWorks Research Laboratory, School of Computing, Universiti Utara Malaysia, 06010 Sintok, Kedah, Malaysia   ABSTRACT Photonic Crystal Fibers (PCFs) have special structures and offer a number of novel design options, such as very large or very small mode areas, high numerical aperture, guidance of light in air, and novel dispersion properties. PCFs have become an attractive field for the researchers and they are trying to work on these to get their properties applied in dispersion related applications, sensing applications and much more. PCFs sensors are widely used in bio-medical applications. The sensitivity and performance of sensors are enhanced due to novel applications of PCFs. This paper outlines a novel design for a generalized biomedical sensor by collaborating PCF and electro-optic effect of Lithium Niobate ( ) based Mach-Zehnder interferometer (MZI) structure. Keywords: Photonic crystal fibers; biomedical sensors; lithium niobate; beam propagation method.  1. INTRODUCTION Photonic crystal fibers are considered as one of the most encouraging elements in optical biosensors due to their enriched performance capacities of being immune to electromagnetic noise, reliable and highly sensitive in comparison with already existing optic fibre biosensors. The sensing application of PCF was first noticed in [1], where absorption spectrum of acetylene filled waveguide was studied. A photonic crystal based sensor allowing detection of individual molecules via their two-photon fluorescence has been described in [2]. PCFs can be used for evanescent-wave sensing of bio molecules, such as DNA or proteins [3-4]. The latest advances in PCFs and micro electro mechanical system (MEMS) offer considerable opportunity to realize an optical endoscope which permits high-resolution visualization of internal organs of body [5-7]. The use of polymer optical fibres permits remarkable composition flexibility of waveguide and sensing features [8]. The polarization-maintaining photonic crystal fiber (PM-PCF) with higher birefringence than already existing polarization-maintaining fibers, allows a smaller length in practical use [9]. Optical switching phenomena using MZIs and its efficient application to perform various digital logic operations in [10-14]. In this paper, a novel generalized biomedical sensor is proposed by collaborating photonic crystal fiber and electro-optic effect of Lithium Niobate ( ) based MZI structure. The proposed device is based on the fact that effective refractive index of a PCF varies on selectively filling the holes of a normal index-guiding solid core. The proposed device is pumped with a 635 nm signal and the return photoluminescence is coupled to the active surface of a light Optical Measurement Systems for Industrial Inspection IX, edited by Peter Lehmann,Wolfgang Osten, Armando Albertazzi G. Jr., Proc. of SPIE Vol. 9525, 95252B© 2015 SPIE · CCC code: 0277-786X/15/$18 · doi: 10.1117/12.2182079Proc. of SPIE Vol. 9525  95252B-1Downloaded From: http://proceedings.spiedigitallibrary.org/ on 06/27/2015 Terms of Use: http://spiedl.org/termsr0 -C-)c000oc0(oLASER Source(635 mn, 2.5 mVO 00000O 0003 000O 000D000O 00TLS001)V mas)SM.F PCF SAIF12.(LDR)Ocnc+7.r --Isa1 Signal_ziI'b +12 V4112 \oCLICR1  dependent regenerated acrsecond electr Figure 1 showfibers of 2	μsweat, saliva,fiber-2 is appincident lightstone bridge, inputs of a diamplifier are obtained at ou      2.1 Design oUric acid is auric acid dissuric acid or istones, diabesistor (LDR),oss the wheaode of MZI. S2s the experim length each sputum etc.)lied to the act. The LDR is so as to creatfferential ampadjusted in sutput of MZI Fig. 1f uric acid co by-product oolves in bloods not able to tes and gout  which is cont stone bridgection 2 expl. WORKIental set up . After that,  inserted in itive surface arconnected as e a potential dlifier, whosech a way thatswitches from: Schematic diancentration f the metabol and reachesremove mostcan be foundnected as one is applied tains the workNG PRINCfor the propoa photonic cs holes is fixeea of a light one of the armifference bet output is app as concentra one port to thgram for expersensor ic breakdown to the kidney of it, many m. In this Secte of the four o inputs of aing principle IPLE OF Esed device. Arystal fiber od in the slot. dependent res of wheat stoween points Plied to secontion level of ae other.  imental set up  of purines, ws. From thereedical condion, design oarms of whea differential of the experimXPERIME gap is createf 2	μ  lengthThe optical oistor (LDR), ne bridge. A 1 and P2. Poid electrode o particular safor a generalizehich are foun it passes outitions like forf uric acid ct stone bridgamplifier, outental set up. NTAL SETd originally in with the boutput obtainewhose resistabattery sourcnts P1 and P2 f an MZI. Thlt exceeds thed bio-medical d in some fo in urine. If thmation of amoncentration e. The potenput of whichUP  between twdy fluid (e.g.d at the end once depends oe is connectedare connectede parameters  specified limsensor. ods and drinke body produmonium acidsensor using tial difference is applied too single mode blood, urinef single moden intensity o across whea to respectiveof differentiait, light signas. Most of theces too much urate kidneyvarious blood   ,  f t  l l       Proc. of SPIE Vol. 9525  95252B-2Downloaded From: http://proceedings.spiedigitallibrary.org/ on 06/27/2015 Terms of Use: http://spiedl.org/terms0.45 -`.. 0.44 -,t' 0.43-..air- 0.42 -t: 0.41 -c),^ 0.400.39- - Electric field intensity2 4 6 8 10Uric acid concentration (mg /dl)12  specimens is discussed. The experimental set-up for the proposed sensor is shown in Fig. 1, except that instead of generalizing the sensor for different applications, air holes of the PCF are filled with a serum specimen. A laser source with a wavelength of 635 nm has been used to generate a beam of light, and then this beam is guided into PCF using a SMF. On filling up the air holes with serum specimens taken from different persons, electric field intensity monotonically decreases with the increase in concentration of uric acid as shown in Fig. 2.                    Fig. 2: Variation of electric field intensity with respect to uric acid concentration (obtained at output of PCF). Light obtained from PCF is incident on an LDR, which is connected as one of the arm of wheat stone bridge. The resistance of LDR decreases as the illuminance ( ( )) increases. The illuminance ( ( )) is given by the relation ( ) = × / / 																																																																																																																																																													(1)  	= 150 lm/W for laser source operating at 635nm. 		 	is the surface area over which the light is incident.	 =1.9625×10  for the LDR used in the experimental setup. The relation between illuminance and resistance of an LDR is given by   = 																																																																																																																																																																																						(2)                              and  are the reference values for illuminace and resistance respectively, values of which are 1000 lux and  400	Ω respectively for the LDR used in our experimental setup. A is in the range from -0.7 to -0.9. So, the resistance of LDR  Proc. of SPIE Vol. 9525  95252B-3Downloaded From: http://proceedings.spiedigitallibrary.org/ on 06/27/2015 Terms of Use: http://spiedl.org/terms2 4 6 8 10Uric acid concentration (mg/d1)12  increases with decrease in illuminance as obtained from Eqn. 2. Figure 3 shows the variation of resistance for LDR with increase in uric acid concentration in serum.  Fig. 3: Graph showing variation of resistance of LDR with increase in uric acid concentration. When the concentration of uric acid is 3 mg/dl, resistance of LDR is equal to75 . Resistances ,  and  are selected in such a way that a null condition is achieved in wheat stone bridge (i.e. 0 Volt potential difference exists between points  and ). This 0 Volt potential is applied to second electrode of MZI [15] via a differential amplifier. As the resistance of LDR varies ( i.e. uric acid concentration increases), wheat stone bridge gets unbalanced and a finite voltage difference is applied to input of differential amplifier, which amplifies the voltage difference (as shown in Table1) according to the relation. =	 ( − )																																																																																																																																																																							(3) Figure 4 shows the voltage obtained at output of differential amplifier with respect to resistance of LDR. When the concentration of uric acid reaches to a particular limit i.e. 11mg/dl, output of differential amplifier reaches 6.80V. At this voltage, output light switches from one port to the other. Thus, the output light intensity is being controlled by the voltage available at the output of differential amplifier, which in turn is calibrated with the concentration of uric acid through wheat stone bridge and a differential amplifier. So, with the help of proposed device, concentration of uric acid in serum can be calculated without need of any other device or measuring equipment.  Proc. of SPIE Vol. 9525  95252B-4Downloaded From: http://proceedings.spiedigitallibrary.org/ on 06/27/2015 Terms of Use: http://spiedl.org/termsIFE-IVoltage at output of OP-AMPII I r I I I75 80 85 90 95 100Resistance of LDR (ohm)  S. No. Uric acid     Conc. ( / ) Non-linear refractive index × 10 /  Electric field at output of PCF ( / )Power at output of PCF (mW) Resistance ( ) Voltage at output of differential amplifier (V) Electric field at first output of MZI 1 3 5.89 0.4472 0.49 75 0 0.04 2 5 8.84 0.4320 0.46 81 1.99 0.44 3 7 12.47 0.4195 0.44 88 3.98 0.78 4 9 14.65 0.4052 0.41 95 5.73 0.95 5 11 17.96 0.3950 0.39 102 6.80 0.99  Figure 5 shows the BPM simulation results for the proposed structure. From the results, it can be clearly seen that for 0 Volt applied to second electrode of MZI, light comes out of second output port of MZI. As the concentration of uric acid goes on increasing, light at second output port goes on decreasing and light at first output port goes on increasing simultaneously. As the concentration reaches its upper limit, all the light gets shifted to its first output port.     Fig. 4: Voltage at the output of differential amplifier with respect to resistance.  Table 1: Variation of different parameters of uric acid concentration sensor  Proc. of SPIE Vol. 9525  95252B-5Downloaded From: http://proceedings.spiedigitallibrary.org/ on 06/27/2015 Terms of Use: http://spiedl.org/terms11J1..fill'OF,ail ?',III_IIIJIM_11I_IlIII_dl'-'11miler'1ÌYIII111III111III111III111III111III111IIIIIIIII111III111NI111x,111'11lir' 111'.i0..IIITIllA1R'_dillAr--diertifUric acid conc. (mg/dl)Uric acid conc. ( mg/dl)Uric acid conc. (mg/dl)1111IElectric field intensityElectric field intensityElectnc field intensitywUric acid conc. (mg. dl)Uric acid conc. (mg/dl)eeeeee_ eElectric field intensityElectric field intensity   Fig. 5: OptiBPM simulation results for the uric acid concentration sensor. 3. CONCLUSION  In this work, a design of uric acid sensor is demonstrated using solid-core photonic bandgap fiber and electro-optic effect of Lithium Niobate ( ) based MZI structure. The proposed design provides the direct value of the concentration of the uric acid in the blood; so, direct measurement of the uric acid concentration is possible at the output. The measurement is performed for a range of 8 mg/dl (from 3 mg/dl to 11 mg/dl). The sensitivity is at its best because of the novel applications of PCFs. By employing the differential amplifier appropriate voltage at the second electrode of the MZI can be provided precisely. The voltage at the second electrode of MZI, (and hence the output intensity of light at the first output port of MZI) is calibrated with the concentration of the uric acid to provide the direct output value. Hence the proposed device is very promising for biomedical sensing applications (uric acid in our case) using optical techniques. Acknowledgement This work is supported by the project entitled “Performance study of some WDM optical network components and design of optical switching devices” under the Faculty Research Scheme of DIT University (Ref. No.: DITU/R&D/2014/7/ECE) undertaken by Dr. Santosh Kumar. The authors would also like to thank Prof. K. K. Raina for encouragement and support during the present research work.    Proc. of SPIE Vol. 9525  95252B-6Downloaded From: http://proceedings.spiedigitallibrary.org/ on 06/27/2015 Terms of Use: http://spiedl.org/terms   References: [1] Dicaire, I., Rossi, A.D., Combrie, S. and Thevenaz, L., “ Probing molecular absorption under slow-light propagation using a photonic crystal waveguide,” Opt. Lett. 37, 4934-4936 (2012). [2] Farrer, R.A., Previte, M.J.R., Olson, C.E., Peyser, L.A. and Fourkas, J.T., “ Single-molecule detection with a two-photon fluorescence microscope with fast-scanning capabilities and polarization sensitivity,” Opt. Lett. 24, 1832-1834 (1999).  [3]  Jensen, J.B., Pedersen, L.H., Hoiby, P.E., Nielsen, L.B., Hansen, T.P., Folkenberg, J.R., Riishede, J., Noordegraaf, D., Nielsen, K., Carlsen, A. and Bjarklev, A., “Photonic crystal fiber based evanescent-wave sensor for detection of biomolecules in aqueous solutions,” Opt. Lett. 29, 1974–1976 (2004). [4]  Jensen, J.B., Hoiby, P.E., Emiliyanov, G., Bang, O., Pedersen, L.H., and Bjarklev, A., “Selective detection of antibodies in microstructured polymer optical fibers,” Opt. Express 13, 5883–5889 (2005). 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Design of photonics crystal fiber sensors for bio-medical applications

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Design of photonics crystal fiber sensors for bio-medical applications

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