Conference Papers in Science
Volume 2015 (2015), Article ID 513621, 8 pages
http://dx.doi.org/10.1155/2015/513621

Conference Paper

Optical pH Detection with U-Shaped Fiber-Optic Probes and Absorption Transducers

Jakub Zajíc,¹ Lenka Traplová,¹ Vlastimil Matějec,² Marie Pospíšilová,¹ and Ivo Bartoň²

¹Faculty of Biomedical Engineering, Czech Technical University in Prague, Kladno 2, Czech Republic
²Institute of Photonics and Electronics AS CR, v.v.i., Chaberská 57, 182 51 Praha 8, Czech Republic

Received 12 December 2014; Accepted 18 February 2015

Academic Editor: José B. Quintana

This Conference Paper is based on a presentation given by Jakub Zajíc at “Meeting on Materials and Their Applications for Devices and Sensors 2014” at “ Meeting on Materials and Their Applications for Devices and Sensors 2014” held from 5 November 2014 to 7 November 2014 in Mahdia, Tunisia.

Copyright © 2015 Jakub Zajíc et al. This is an open access article distributed under the Creative Commons Attribution License, which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly cited.

Abstract.

In medicine knowledge of pH values can provide us with information not only about the patients’ status but also about physiological processes in the patient’s body. Measurements of pH in small-sample volumes and online pH monitoring in vivo can be employed to obtain such information. For such measurements we have developed and investigated U-shaped fiber-optic probes with immobilized pH indicators in this paper. U-shaped probes with a diameter of about 2 mm were prepared. Three different pH indicators, methyl red, methyl orange, and bromothymol blue, were immobilized in two types of matrices, namely, porous silica (PS) and ethylcellulose (EC), and applied on the U-shaped probes. Changes in spectra of transmitted power were measured and calibration curves were determined from these spectra. It has been found that a working pH range of prepared probes was from 3.1 to 7.6. The maximum sensitivity was about 0.1 1/pH unit. Effects of structural relaxations of detection layers and indicator leaching observed in experiments are discussed.

1. Introduction

Measurements of pH are broadly employed in industry, agriculture, biology, or medicine. In medicine pH of various body fluids such as urine, blood, gastric acid, or saliva is measured. Values of pH within or out of normal physiological pH ranges typical for these body fluids (e.g., from 7.35 to 7.45 for blood) can give us information about a patient’s medical status. A number of medical studies have been published which were related, for example, to the monitoring of esophageal pH [1], fetal pH monitoring [2], and venous and arterial blood pH monitoring [3].

In order to measure pH, different sensors including electrical and optical ones are used [4]. So far most of the investigated and developed optical pH sensors employ absorption or fluorescence pH indicators [5] which interact with protons and change their optical properties due to such interactions [4]. A refractive-index based pH sensor has also been developed [6]. Polymeric or sol-gel detection membranes have been used for the immobilization of pH transducers or for proton and other ion adsorptions [4, 6, 7].

Different sensing platforms of optical pH sensors have been investigated [4], such as planar sensors or fiber-optic sensors. Fiber-optic pH sensors are usually based on the evanescent-wave and reflection principles [4, 8–11]. Mainly reflection-based sensors have been commercialized [4]. Such sensors have been used in medicine [11], for example, for monitoring gastroesophageal reflux, because they are small and can be easily inserted into medical catheters.

Several approaches have been tested in order to increase the response of evanescent-wave fiber-optic pH sensing probes [12–14]. They include mode filtering [12], etching a multimode sensing fiber to open the access to the core-cladding boundary [13], and bending the probe fiber to a U shape [14–16]. U-shaped evanescent-wave probes offer us several advantages over straight ones such as enhanced sensitivity and small dimensions which could be used in pH sensors for medicine [14]. However, only one paper [14] presents results determined with absorption pH transducers immobilized in a detection membrane.

This paper presents results of the investigation of U-shaped probes provided with three different absorption pH indicators, namely, methyl orange, methyl red, and bromothymol blue. The indicators were immobilized in the probe cladding by using matrices of porous silica or ethylcellulose. Spectral responses and calibration curves of the probes are reported.

2. Experiment

2.1. Fabrication of U-Shaped Probes

U-shaped sensing elements were prepared from segments of polymer clad silica (PCS) fibers with silica core diameters of 400 μm and lengths of about 50 cm. The fibers were prepared at the Institute of Photonics and Electronics. In each preparation the original optical cladding of dimethylpolysiloxane polymer was removed from the central part of the segment in a length of about 5 cm. For this removal the segment was immersed in an aqueous solution containing hydrofluoric acid for about five minutes and the swelled cladding was mechanically stripped. The bare silica core was shortly dipped into a solution composed of hydrofluoric and nitric acids and rinsed with water. Then the center of this bare part was carefully heated in an oxyhydrogen burner flame and manually bent to an arch with a diameter of about 2 mm. In order to fix arch dimensions, the segment arms coated with the polymer cladding were inserted into a small glass tube and glued in it using a silicone adhesive. Then the bent part was dipped in the solution of hydrofluoric and nitric acids, rinsed in water, and dried in air. Detection layers containing pH indicators were applied on the bare parts of such detection elements.

2.2. Preparation of Detection Layers

Three pH indicators, namely, methyl orange (a pH detection range of 3.1–4.4 in aqueous solutions), methyl red (a pH range of 4.4–6.2 in aqueous solutions), and bromothymol blue (a pH range of 6–7.6 in aqueous solutions), have been investigated. Powders of the indicators were purchased from Sigma-Aldrich, Czech Republic. These indicators were immobilized in matrices prepared from alkoxide, tetramethylorthosilicate (TMOS), or polymer and ethylcellulose (EC). Chemicals were purchased from Sigma-Aldrich, Czech Republic.

Alkoxide-based detection layers were fabricated by the sol-gel method from input alkoxide sols. In experiments a starting sol was prepared from TMOS ( = 1 mol/L), ethanol as a solvent, nitric acid as a catalyst and water (water/alkoxide ratio = 1.5) at first. The sol was aged at 70°C for 1 hour while being stirred. The composition of the sol was selected on the basis of results reported elsewhere [17, 18]. Each input sol was prepared by dissolving a particular indicator in the starting sol. On the basis of bulk absorption spectra measurements, concentrations of 0.1, 0.5, and 0.5 g/L were used for methyl red, methyl orange, and bromothymol blue, respectively. The input sols were applied onto the U-shaped elements by dip-coating technique (withdrawing speed of 10 cm/min). Applied gel layers were dried at 90°C for 24 hours. A thickness of about 0.3 μm and a refractive index of about 1.42 can be estimated for such detection layers on the basis of previous experiments.

Ethylcellulose detection layers were prepared by using an approach reported elsewhere [19]. Two input solutions A and B were prepared at first. Solution A contained one of the particular pH indicators at a concentration of 0.6 g/L, tetraoctylammonium hydroxide (TOAH), and methanol. Solution B contained ethylcellulose 15 wgt.% in 80 mL of toluene and 20 mL of ethanol. A final solution used for coating was mixed from 1 mL of solution A, 10 g of solution B, TOAH, and tributyl phosphate. The final solution was applied on U-shaped elements by dip-coating technique (withdrawing speed of 10 cm/min) and dried at 80°C for 1 hour. For these detection layers a thickness of about 3 μm and a refractive index of about 1.49 can be estimated from measurements on glass slides.

2.3. Absorption Spectra of Indicator Solutions

Absorption spectra of the indicators in different aqueous solutions were measured in a range of 200–1100 nm and used as a reference to those determined by using U-shaped detection probes. For such purpose a PerkinElmer Lambda EZ210 spectrometer and a cuvette with a path of 1 cm were used. Test solutions of hydrochloric acid with concentrations of 10⁻¹–10−4 mol/L, acetic buffer solutions mixed of acetic acid and sodium acetate, and Sorensen buffer solutions mixed of potassium and sodium phosphates were used. Values of pH of such solutions were determined electrochemically by using a pH meter Jenway 3306. The indicators were dissolved in the measured solutions in a concentration of 0.05 g/L.

2.4. Characterization of U-Shaped Detection Probes

Transmission spectra of prepared U-shaped detection probes were measured by using a setup schematically shown in Figure 1. The setup consisted of a halogen lamp Ocean Optics HL 2000 as a light source and an Ocean Optics USB 650 diode array spectrometer as a detector. An integration time of 100 ms and averaging of three spectra allowed us to measure the output power with an accuracy of about 30 arb. units. In experiments tested fibers were joined to the detector via an FC connector. The input part of the fiber was fixed in a holder that enabled directing light beams from the source into fibers under beam inclination. Such an arrangement was used to further increase the detection sensitivity. Angles of inclination of about 30° were used. Tested U-shaped elements were immersed in the test solutions with different pH and spectral output powers from tested fibers were measured in a range of 350–1100 nm.

Figure 1: Scheme of the experimental setup for characterization of U-shaped probes.

3. Results and Discussion

A photo of one prepared U-shaped element is shown in Figure 2. Light from a red-laser pointer was directed into the right arm of the element to highlight the probe.

Figure 2: Photo of a U-shaped fiber element; onset: details of the element arc.

Figure 3 shows spectra of output power from a U-shaped element without any detection layer. A decrease of the output power caused by immersing the element in water can be explained by a refractive-index change from air (a value of about 1) to water (a refractive index of about 1.33).

Figure 3: Output powers of a U-shape fiber without a detection layer in air and in water.

Bulk absorption spectra of the tested indicators measured for different pH values are shown in Figures 4(a)–4(c). All the spectra show absorption bands which can be attributed to basic and acidic forms of the indicators. Thus, for methyl red one can conclude from Figure 4(a) that the acidic indicator form, that exists at lower pH values, absorbs light at about 550 nm while the basic one, that is present at at higher pH values, absorbs light at about 430 nm. In the case of methyl orange the band of the acidic form is centered at about 520 nm and that of the basic form at about 450 nm (see Figure 4(b)). The indicator bromothymol blue has the absorption band of its basic form centered at about 630 nm and the acidic form absorbs light at about 450 nm as one can see from Figure 4(c).

(a)

(b)

(c)

Figure 4: Bulk absorption spectra of indicator solutions at different pH; (a) methyl red, (b) methyl orange, and (c) bromothymol blue.

Spectra of output power measured for different pH with a U-shaped element coated with the detection layer of methyl red in ethylcellulose are shown in Figure 5(a). The element was immersed in solutions of hydrochloric acid and in acetic buffer solutions. By comparing curves in Figure 4(a) with those in Figure 5(a) one can conclude that there are power changes in a spectral range from about 600 to 1000 nm which cannot be attributed to spectral changes of methyl red. They can be explained by relaxation changes of the ethylcellulose matrix, i.e. by changes of its refractive index. Spectral changes related directly to methyl red changes can be identified in a range of 480–600 nm. Taking values of the output power at a wavelength of 590 nm and plotting them against the pH values, measured electrochemically, calibration curves in Figure 5(b) can be drawn with a reference of an ethylcellulose layer without methyl red. Such curves were obtained by fitting experimental data with a sigmoidal Boltzmann curve [20]. The curves in Figure 5(b) show that methyl red in the ethylcellulose matrix can be used for pH detection in a pH range of 3–5.5. The different calibration curves for different measurements in Figure 5(b) can be explained by relaxation changes in the layer. Some leaching of the indicator can be concluded from slightly different slopes of the calibration curves for different measurements. A detection sensitivity of about 0.01–0.02 1/pH unit can be determined from Figure 5(b).

(a)

(b)

Figure 5: (a) Output power from U-shaped probe coated by detection layer of methyl red in ethylcellulose; (b) calibration curves of the U-shaped probe for repeated measurements.

Experimental results determined with a U-shape probe coated with the layer of methyl red in porous silica are shown in Figures 6(a) and 6(b). The probe was immersed in the acetate buffer solutions. In this case a different evaluation approach was used that consists in using output power measured with the layer in water as the reference and in normalizing the resulting spectra to the methyl red isosbestic point at 480 nm. It is expected that such an approach could suppress relaxation changes. Difference spectra in Figure 6(a) show two bands of methyl red, one at about 430 nm and the other at about 570 nm. On the basis of the spectra in Figure 4(a), in Figure 6(a) the band at 430 nm can be attributed to the methyl red basic form and that at 570 nm to the acidic indicator form.

(a)

(b)

Figure 6: (a) Normalized absorption spectra measured on a layer of methyl red in porous silica applied on a U-shaped probe; (b) calibration curves of the coated U-shaped probe at 560 nm.

Taking values of the absorbance at 560 nm from Figure 6(a) and plotting them against pH values measured electrochemically, the calibration curves in Figure 6(b) were drawn. They show that the probe has a linear response in a pH range from 3.8 to 6.5. A sensitivity of about 0.03 1/pH unit can be estimated from the calibration curves.

Spectra of output power from a U-shaped element coated with the detection layer consisting of bromothymol blue in ethylcellulose are shown in Figure 7(a). Sorensen buffer solutions were used for the probe tests. In this case a power dip centered at about 630 nm can be attributed to the basic form of bromothymol blue. Taking output power values at 630 nm from Figure 7(a), calibration curves in Figure 7(b) can be drawn with a reference of an EC layer without bromothymol blue. The curves in Figure 7(b) show that bromothymol blue in the EC matrix can be used for pH detection from pH = 6.2 to pH = 8. A maximum detection sensitivity of about 0.15 1/pH unit can be determined from Figure 7(b) (first measurement). However, from Figure 7(b) it is also evident that the element response and sensitivity substantially dropped down when the measurement was repeated (cf. 1st and 2nd measurements). Such results can be explained by leaching of the indicator from the layer. The swelling of the detection layer in Sorensen buffer solutions also takes place.

(a)

(b)

Figure 7: (a) Spectral output power from a U-shaped element provided with a layer of bromothymol blue in ethylcellulose; (b) calibration curves of the U-shaped probe for repeated measurements at 630 nm.

Spectra of output power measured with a U-shaped probe coated by the detection layer of bromothymol blue in porous silica immersed in different Sorensen buffer solutions were also measured. They were similar to those shown in Figure 7(a); however, a spectral dip attributed to bromothymol blue was smaller. Calibration curves determined from the measured spectra are shown in Figure 8 for a wavelength of 655 nm and a reference of an EC layer without bromothymol blue. These curves show that the probe has a linear response in a pH range from 6.6 to 7.5. The sensitivity of about 0.04 1/pH unit can be estimated from the calibration curve for 1st measurement that decreases to about 0.005 1/pH unit for 2nd measurement. The indicator leaching and relaxation changes in the detection layer can explain differences between the calibration curves for 1st and 2nd measurements.

Figure 8: Calibration curves of a U-shaped probe coated with detection layer of bromothymol blue in porous silica for repeated measurements at 655 nm.

A set of experiments was made with a straight PCS fiber segment coated with a detection layer of bromothymol blue in ethylcellulose prepared at the same condition as that on the U-shaped probe. A maximum sensitivity of about 0.007 1/pH unit was determined from measured response curves. This value shows that bending a detection probe to a U shape is related to a sensitivity increase.

Spectra of output power from a U-shaped element coated with the detection layer of methyl orange in ethylcellulose for different pH values are shown in Figure 9(a). Responses of probes with this indicator were tested by immersing the probe in solutions of hydrochloric acid. By taking into account the curves in Figure 4(b) one can conclude that spectral changes related directly to methyl orange changes are in a range of 400–600 nm and that there are power changes related to the layer relaxation at longer wavelengths.

(a)

(b)

Figure 9: (a) Spectra of output power from a U-shaped element provided with a layer of methyl orange in ethylcellulose; (b) calibration curves of the U-shaped probe for repeated measurements at 590 nm.

Taking values of output power at a wavelength of 590 nm, calibration curves in Figure 9(b) can be drawn with a reference of an ethylcellulose layer without methyl orange. The curves in Figure 9(b) show that methyl orange in the ethylcellulose matrix can be used for pH detection in a pH range of 3–4.5. Similarly as with the previous pH indicators the element response was changed when experiments were repeated due to swelling of the detection layer. In this case the leaching of the indicator from the detection layer is not probably strong because the curve slopes in Figure 9(b) do not differ much for 1st and 2nd measurements. The sensitivity of about 0.005 1/pH unit can be determined from Figure 9(b).

Similar spectra of output power as those in Figure 9(a) were measured with a U-shaped probe coated by the detection layer of methyl orange in porous silica. Calibration curves at 540 nm determined from such spectra are shown in Figure 10 with a reference of a porous silica layer without methyl orange. The sensitivity of about 0.03 1/pH unit can be estimated from the calibration curve for a pH range from 3.2 to 4.5 (Figure 10, the black line). However, this sensitivity decreases to about 0.015 1/pH unit when the calibration is repeated (see Figure 10, the red line).

Figure 10: Calibration curves of the U-shaped probe for repeated measurements at 540 nm, methyl orange in porous silica.

As the used measurement setup did not allow us to do time-response measurements at a particular wavelength the time response of the probes could be only estimated from measured spectral responses. It has been found that when a U-shaped detection probe was immersed into a tested solution an output power changed quickly within approximately one minute. The output power changed much slowly after more than 5–10 min. Thus, a short immersion of the probes in testing solutions on a level of 1–3 min was used in all experiments.

Experimental results discussed above show that U-shaped fiber-optic probes, fabricated from PCS optical fibers, can exhibit the sensitivity to pH provided that colorimetric pH indicators are applied onto their bent part. By comparing results of the measurements on bulk solutions (see Figure 4) with those made by the U-shaped probes (Figures 5–9) one can see that the probes exhibit lower responses to pH changes. The detection sensitivity also decreases from about 0.3–0.4 1/pH unit to 0.005–0.15 1/pH unit (for first measurements). This sensitivity decrease can be explained by a ratio of power in the evanescent field of fiber-optic sensors on a level from 0.005 to 0.05. In the case of the U-shaped probes it has also been found that such probes are sensitive to refractive-index changes related to relaxation changes (swelling) of detection layers. Such relaxation changes induce baseline changes of measured spectra and consequently influence the spectral response of probes caused by pH indicators. It has also been observed that some colorimetric indicators such as bromothymol blue can leach out from detection layers of ethylcellulose in aqueous solutions which decreases the detection sensitivity.

4. Conclusions

It has been found that U-shaped fiber-optic probes coated with three types of absorption pH indicators, namely, methyl orange, methyl red, and bromothymol blue, can be used for pH detection in a pH range from about 3 to 7.6 in aqueous solutions. It has been proved that the indicators can be immobilized in matrices of porous silica or ethylcellulose. These matrices, however, exhibit some relaxation changes which complicate the interpretation of measured experimental data. The approach has been developed that is based on normalizing sensor responses to those determined at isosbestic points of used indicators and which, to some extent, can suppress such relaxations. This approach needs to be further improved as well as the composition of matrices of detection layers. Bromothymol blue leaching has been observed which can decrease the detection sensitivity from 0.15 1/pH unit to about 0.02–0.03 1/pH unit when detection experiments are repeated. These effects will be further investigated. Such U-shaped pH detection probes are expected to find use at pH measurements on small volumes of aqueous samples in medicine and biology.

Conflict of Interests

The authors declare that there is no conflict of interests regarding the publication of this paper.

Acknowledgment

This work was financially supported by the Project “BIO-OPT-XUV Research Team Advancement” at the Faculty of Biomedical Engineering, CTU, Prague, no. MEYS ESF Project CZ.1.07/2.3.00/20.0092.

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