Fluorescence lifetime-based sensing of sodium by an optode †

We report a 1,2,3-triazol fluoroionophore for detecting Na + that shows in vitro enhancement in the Na + -induced fluorescence intensity and decay time. The Na + -selective molecule 1 was incorporated into a hydrogel as a part of a fiber optical sensor. This sensor allows the direct determination of Na + in the range of 1–10 mM by measuring reversible fluorescence decay time changes.

Sodium plays a crucial role in many physiological processes and the Na + concentration largely differs in intra-and extracellular compartments. The concentration of intracellular free Na + is in the range of 5-30 mM, whereas that of extracellular is more than 100 mM. 1 For the determination and visualisation of intra-or extracellular Na + levels, Na + -responsive fluorescent probes are suitable tools. Minta and Tsien designed the first fluorescent indicators for detecting cytosolic Na + (B30 mM) with dissociations constants K d o 50 mM. 1 Several Na + -sensitive fluorescent probes are commercially available, e.g. SBFI (sodium-binding benzofuran isophthalate) (K d B 11 mM), 1,2 Sodium Green (K d B 21 mM), 2 CoroNa Green (K d B 80 mM) 2,3a and CoroNa Red (K d B 200 mM). 2,3b Furthermore, photoinduced electron transfer (PET)-type fluoroionophores have been proven to be successful as highly selective sodium sensing molecules. [4][5][6] For the analysis of sodium in serum and whole blood (B140 mM) He et al. designed a PETfluoroionophore which consists of a N-(o-methoxyphenyl)aza-15crown-5 ionophore (K d B 80 mM) and a 4-aminonaphthalimid fluorophore. 4 An application of this fluoroionophore is the use in clinical diagnosis as a part of optical sensors for analytes such as Na + in whole blood. 7 For the continuous sensing of Na + , several optodes based on fluorescence intensity changes have been developed (e.g., to be used in films or beads). 8a-n Many of these optode layouts are based on a general concept, in which the detection of the targeted analyte and the optical signal generation are separated. The analyte (here Na + ) is bound and induces an ion exchange which subsequently is detected by a pH-sensitive dye. The advantage of such an approach is that the optical part of the sensor can be applied to many different analytes. However, the optodes can be cross-sensitive to pH changes in the samples. To date, there has been no fiber-optical sensor for direct Na + sensing (e.g., on the basis of a PET-fluoroionophore) incorporated in a hydrogel using fluorescence decay time changes as the detection principle.
Sensor endurance is also a major challenge in general. 9 Concepts often rely on the ratiometric measurements of intensities or are based on fluorescence decay time determination. These two sensing schemes are independent of the probe concentration and aging effects of the optode (e.g., due to photobleaching). For monovalent ions such as sodium and potassium, it is difficult to develop ratiometric fluoroionophores, 10 and only a few fluorescence decay time based probes for Na + are available, such as Sodium Green. 11 There is a fast increasing demand for tailored fluorescence probes (with respect to e.g., the spectral range, analyte or photostability) in life sciences. Here, among others, sodium is one of the top analytes and the development of a novel fluorescent probe based on the detection of changes in the fluorescence decay time is desirable. Developing a sensing scheme for the direct detection of sodium based on fluorescence decay time measurements will not only minimize the cross-sensitivity for pH and enhance the overall performance of the sensor with respect to aging effects but will also add another dimension (decay time in addition to spectral parameters) to the analysis, which will be beneficial for the development of multianalyte sensing schemes. Overall, the development of new optical sensor devices with (a) suitable K d values for extracellular/ blood or intracellular sodium measurements, (b) an excellent selectivity over physiological potassium concentrations, (c) no pH interference in the physiological pH range, (d) a fast response time, (e) a reversible signal change, and (f) a change of the fluorescence decay time is the focus of attention at present.
Recently, we found that in CuAAC (Cu(I)-catalyzed 1,3-dipolar azide alkyne cycloaddition) reaction generated fluoroionophores, the electronic conjugation of a N-phenylaza-18-crown-6 12a or of a N-(2-methoxyethoxyphenyl) aza-18-crown-6 12b ionophore and a 7-diethylaminocoumarin fluorophore through a 1,2,3-triazol-1,4-diyl p-linker results in a perfect signal transduction chain for the exclusive sensing of K + under simulated physiological conditions. 12a,b Thereby, we prepared a fluorescent membrane sensor by incorporating the N-(2-methoxyethoxyphenyl)aza-18crown-6-fluoroionophore into a hydrogel, which showed fast and fully reversible fluorescence intensity changes in the range of 1-10 mM potassium. 12b In this communication, we have maintained the signal transduction chain: aniline-triazole-coumarin in the construction of Na + -sensitive PET-fluoroionophores 1 and 2 (Scheme 1). Thus, for selective Na + binding the N-(o-methoxyphenyl)aza-15-crown-5 ionophore 4,6d was selected owing to its excellent selectivity for Na + over K + in the range of 100-180 mM. Herein, in Tris buffer Na + induces fluorescence intensity and decay time enhancement in 1 or 2. When 1 was embedded in the hydrogel poly(2-hydroxypropyl)methacrylate (PHPMA), we found a reversible change in the decay-time and intensity, obtained from fiber-optical fluorescence measurements. To the best of our knowledge, it is the first fiberoptical sensor for Na + sensing based on a combination of a PETfluoroionophore and of the PHPMA hydrogel using fluorescence decay time changes as the fundamental detection principle.
The selectivity of 1 for Na + over K + in the physiological range is shown in Fig. S3c (ESI †). The K d value of 1 for K + is B276 mM and of 2 for K + is B1060 mM (Fig. S6a and b, ESI †), indicating that 1 is B3-fold more selective for Na + than for K + and 2 B4-fold more selective.
To investigate the pH-sensitivity of 1 and 2, the fluorescence intensity was measured in H 2 O at different pH values (see ESI †). The resulting pK a of 1 is 4.9 and that of 2 is 4.6, respectively. 1 and 2 are unaffected in the physiological relevant pH range of 6-8 (Fig. S8, ESI †).
Due to the underlying PET process in 1, the observed fluorescence kinetics are complex. The fluorescence decay curves at l em = 500 nm could be reasonably well fitted using a bi-exponential decay kinetics yielding main decay times of 0.08 ns (90%) for 1 and 0.39 ns (99%) for 1 + 180 mM Na + (Table S1, ESI †). During complexation of Na + the fraction of the short fluorescence decay time (0.08 ns) component decreases and the average fluorescence decay time increases (Fig. 1b) as the fraction of the longer fluorescence decay time increases. The K d value of 1 + Na + calculated based on the average fluorescence decay time is B15 mM (see ESI †). The fluorescence decay times of 1 were only slightly affected by K + ions (see Table S1, ESI †). Furthermore, we observed for 2 + Na + a similar decay time behaviour as found for 1 + Na + (Table S1, ESI †).
Probe 1 was selected for studies on its application as a Na + -sensor because it showed a higher Na + /K + fluorescence response than probe 2. To apply 1 in a sensor membrane for continuous monitoring of Na + concentrations in liquid streams, such as blood, we incorporated it into a polymer matrix. The PHPMA hydrogel is a convenient polymer for making stable membrane sensors. 14a,b For immobilisation of 1 within the hydrogel, both were dissolved in EtOH. This homogeneous mixture was used for film and optode preparation (see ESI †). Firstly, we prepared films of the mixture on glass slides, which we placed in standard cuvettes. The concentration of 1 in these films was 3.75 Â 10 À5 M. In order to avoid difficulties inherent to fluorescence intensity based measurements (vide supra), we determined Na + -induced fluorescence decay time changes by timecorrelated single photon counting (TCSPC). In the hydrogel we found a fluorescence decay time t f of 2.1 ns for 1, which is distinctly longer than that observed in solution (see Table S1, ESI †). In solution the decay time is faster than that in the fixed polymer, because the rate constant of quenching by radiationless processes is larger. The decay time t f increases from 2.1 ns in 10 mM Tris buffer to 2.7 ns in the presence of 140 mM Na + . The K d value determined by TCSPC measurements of 1 for Na + is 42 mM in the PHPMA polymer (see Fig. S12, ESI †).
In the next step we investigated the t f behaviour of 1 in a PHPMA film using a low-cost frequency-domain spectrometer (FD-S) suitable for in situ applications. Therefore, we prepared a PHPMA-based film with a higher dye concentration of 1 (c = 7.5 Â 10 À4 M) which is needed for the FD-S set-up due to sensitivity requirements. We found decay times for 1 (t f = 2.2 ns) and 1 + 100 mM Na + (t f = 2.9 ns) in PHPMA by FD-S (see Fig. S13, ESI †) comparable to the TCSPC measurements, but the K d value of 1 + Na + decreases to 1.6 mM. Due to the higher dye concentration in the polymer matrix the sensitivity to sodium seemed to increase. The K d value of 1 + K + in PHPMA is 6355 mM (Fig. S13, ESI †) indicating the highly improved Na + /K + selectivity of the sensor film.
Finally, in order to further develop this outstanding Na +selective film into an optode for fiber-optical measurements ( Fig. S10 and S11, ESI †), fluorescence intensity and decay time measurements were successfully carried out. The fluorescence intensity increases upon dipping the optode in Na + solutions of different concentrations up to 50 mM (see Fig. 2a). The K d value of 1 + Na + based on intensity changes determined by the optode is 6 mM. Comparable results were obtained by using FD-S. Here, the K d value of 1 + Na + is 2.4 mM using this fiber-optical sensor (see Fig. 2b). Consequently, this optode allows determination of Na + by fluorescence decay time measurements in the range of 1-10 mM.
Furthermore, for continuous sensing of Na + in the range of 1-10 mM by measuring fluorescence intensity and decay time changes of this optode we tested the reversibility. As a proof of principle our first results for continuous Na + sensing are shown in Fig. S17 (ESI †). The response time of the optode after switching the solution from 0 mM Na + to 10 mM Na + during a time period of 2 h shows a good reversible behaviour. The response time depends on the direction of the change: by increasing the sodium concentration the response is faster (o8 min) than by decreasing the concentration (15 min). Here, the layout of the optode (the thickness of the polymer and the concentration of the probe) is a key parameter in this respect and will be further improved in order to reduce the response time. In summary, we have synthesised two regioisomeric fluoroionophores 1 and 2 for Na + by ''click'' chemistry. In solution they showed different K d values (1 + Na + B120 mM and 2 + Na + B260 mM) under simulated physiological conditions. Probe 1 is a capable fluoroionophore for the selective determination of extracellular Na + levels by measuring fluorescence intensity changes. Further, 1 was incorporated into a membrane sensor consisting of a polymethacrylate hydrogel and, in this form, it enabled the continuous monitoring of Na + (1-10 mM) with a reversible response based on fluorescence decay time measurements. Overall, we have shown the first reversible fiber-optical sensor for Na + ions utilizing fluorescence decay time changes. Further studies to improve the brightness, photostability, Na + -induced overall fluorescence decay time changes and the response time of our optode are currently underway in our laboratories.