Edinburgh Research Explorer pH sensing through a single optical fibre using SERS and CMOS SPAD line arrays

: Full exploitation of fibre Raman probes has been limited by the obstruction of weak Raman signals by background fluorescence of the sample and the intrinsic Raman signal of the delivery fibre. Here we utilised functionalised gold nanoshells (NS) to take advantage of the surface-enhanced Raman spectroscopy (SERS) effect to enhance the pH responsive spectrum of 4-mercaptobenzoic acid (MBA). However, the fibre background is still dominant. Using the photon arrival time-resolving capability of a CMOS single-photon avalanche diode (SPAD) based line sensor, we recover the SERS spectrum without a fibre background in a 10 s measurement. In this manner, pH sensing through a multimode fibre at a low excitation power that is safe for future in vivo applications, with short acquisition times (10 or 60 s), is demonstrated. A measurement precision of ± 0.07 pH units is thus achieved. were prepared for functionalisation by centrifugation at 5500 rpm for 10 min. Following centrifugation all or as much as possible of the supernatant was removed without disturbing the pellet. For functionalisation, the pellet was resuspended with distilled water (900 µL) and 4-MBA (100 µL, 1 mM in EtOH) and the samples were left overnight. The NS were washed to remove unbound molecule by centrifuging at 5500 rpm for 10 min. Following centrifugation all or as much as possible of the supernatant was removed without disturbing the pellet. The functionalised particles were then resuspended with 500 µL dH 2 O and the samples were sonicated and vortexed to force the particles back into suspension. This washing procedure was repeated a total of 3×. Following washing the particle suspensions were centrifuged at 5500 rpm for 10 min and 450 µL of the supernatant was removed. The final volume remaining in each of the aliquots was measured by pipette and noted. Samples were again centrifuged at 5500 rpm for 10 min and the appropriate volume of supernatant was removed from each to leave a final volume of 5 µL. The individual aliquots (5 aliquots) were then combined to give a particle suspension with a final volume of 25 µL.


Introduction
Raman spectroscopy, based on exploiting the inelastic scattering of light from a sample, is often used for histochemical analysis such as discrimination of malignant and benign tissue [1][2][3]. The advantages for in vivo investigations are that it is non-destructive and minimally invasive, exhibits high spatial resolution, is chemically sensitive and has a rapid response which is important for in situ diagnosis [4]. However, the small cross section of the Raman scattering results in a weak signal, especially when exciting in the near-infrared regime ( 4 1/ λ -dependency). The signal is often further obscured by fluorescence from surrounding regions e.g. tissue in medical applications. Additionally, in vivo measurements require optical fibre probes to reach the position of interest in the body. The optical fibre exhibits a high Raman scattering from the core material which contrary to other fluorescence background, is constant and scales with the fibre length itself [5,6]. This combination of unwanted background signals makes in vivo Raman spectroscopy extremely challenging, especially with a miniaturized fibre probe.
Efforts in recent years in response to the challenge have included methods of fluorescent background suppression [7]. However, while some are not applicable for in vivo applications, others suffer from sophisticated and expensive set-ups or long acquisition times. Meanwhile several commercial and non-commercial fibre Raman probes have been developed with methods for background suppression ranging from advanced fibre designs [8][9][10] to complex correction methods [11].
We demonstrate a time-correlated single photon counting (TCSPC) [12] spectrometry technique in combination with surface-enhanced Raman spectroscopy (SERS) [13] to overcome the challenges and enable a background free Raman spectrum with an ultraminiaturised single fibre probe. The size and simplicity (moving the advanced and costly apparatus outside the fibre probe) enables endoscopic application in size restricted regions (e.g. the distal lung) with a disposable sensing probe. We exemplify the system for pH sensing with 4-mercaptobenzoic acid (MBA). pH is a key marker for the acid-base balance in metabolism which is tightly regulated but can be locally changed by pathologies such as inflammation and cancer. As an example, generation of an acidic environment increases growth of bacteria and inhibits antibiotics [10]. Quantifying and monitoring the environmental pH in vivo as enabled by this work has potential to improve diagnostics and therapy.
In this paper, we produce a sensing probe through the deposition of MBA functionalised gold nanoshells (NS) on the tip of the delivery fibre optic [10,14]. The gold NS have been designed as optical nanosensors for localized measurements of pH in vivo. They are robust, designed for use in the near-infrared spectral region, avoiding distortion from excessive autofluorescence from tissue and blood, and exhibit a continuous signal over a wide range of pH [15].
We remove fluorescent and fibre backgrounds through post-processing time-gating using the TCSPC capabilities of a complementary metal-oxide semiconductor (CMOS) singlephoton avalanche diode (SPAD) based line sensor. We exploit the different time profiles of background fluorescence, fibre Raman scattering and the SERS signal to separate signal from background [16][17][18][19].
The TCSPC capable CMOS SPAD line sensor detects single photons and generates histograms according to their arrival time for 256 pixels simultaneously which are correlated to different wavelengths [20]. The advantages are high efficiency [21] and high time resolution (< 500 ps time stamping resolution) to record luminescent kinetics down to the nanosecond regime. This enables the utilisation of low excitation power (< 1 mW) and short exposure times (10 s -60 s) thus enabling further development towards the in vivo sensing of physiological parameters. The technique is only limited by photon statistic constraints known as counting loss and pile-up, and inherent limitations on the performance of the SPADs; detector dead-time, dark count rate, varying photon detection probabilities, crosstalk and afterpulsing [12]. The exploitation of this advanced measurement system enables suppression of the unwanted background in the fibre-based Raman probe, facilitating the recovery of the background free spectrum. We demonstrate how this enables low power, rapid pH sensing through a multi-mode fibre with functionalised gold NS achieving improved measurement precision.

Optical setup
The measurements were performed using the time-resolved spectrometer shown schematically in Fig. 1. It consists of four parts: i) The excitation source was a 785 nm pulsed laser (LDH-D-F-N-780 and PDL 800-D, PicoQuant, spectral FWHM < 0.35 nm). The laser when operated at maximum power has a short leading pulse with a FWHM of 30 ps as stated in the manual specific to this laser, however it exhibits a long tail with a FWHM of 1.5 ns containing ¾ of the power. The average power was reduced with neutral density filters to 0.8 mW, this is safe for in vivo measurement and below the damage threshold for the sensors in continuous operation. The repetition rate was 20 MHz, as such, a full measurement of light transiting the length of a 2.7 m fibre and being backscattered to the detector was completed before the next laser pulse. ii) An optical coupling and collection system which was based on the same arrangement as standard for epi-fluorescence measurement. iii) A spectrometer based on a collimation lens, f = 50 mm, a transmission grating (1624 grooves / mm, Wasatch) and a focusing lens, f = 30 mm (both Achromat Doublets, Thorlabs), ensuring a spectral range of 80 nm across the line array centred at 870 nm and a throughput of 78%, measured with a photodiode (S120C Thorlabs). iv) The in-house made CMOS SPAD sensor consisted of 256 pixels in a single line manufactured with 130 nm CMOS technology. The sensor timestamps the single photon events internally and simultaneously for all pixels. For further information about this sensor see [22,23]. This and the lack of any scanning element [16,17], for scanning along the spectral or temporal axis, ensures short measurement times. The dispersion was 0.3 nm/pixel and the spectral resolution was 1.6 nm or 25 cm −1 , limited by entrance slit width, grating density and lens combination. The temporal resolution set by the time-to-digital converter (TDC) was 423 ± 3 ps. The signal level was kept low to ensure a detector count rate of < 1% of the laser excitation rate and < 50% of the detector readout frame rate. The fibrecoupled design is extremely versatile and flexible for a broad range of applications and with the potential to be compact and mobile, suitable for in situ applications.
Two lengths of delivery optical fibres were used to act as passive fibre sensors with functionalised gold NS deposit at the fibre tip: a 2.7 m and an 18 m multimode fibre (both FG050LGA, Thorlabs). The protocol for the SERS preparation can be found in Section A.2.

Data analysis
Utilizing the experimental setup and procedure outlined, a single measurement yields a 2dimensional data array consisting of the spectral axis, the temporal axis and intensity data in terms of number of counts per pixel and per time bin. For gathering the spectral information, each pixel is correlated to a certain wavelength range. The temporal information is gained by measuring the arrival time of the photons and histogramming them for each pixel with the onchip TCSPC functionality of the sensor.
"Noisy pixels" exhibit excessively high dark count rates due to fabrication variations and being electronically closer to their avalanche condition. The data of these pixels are removed from the measurement to avoid introducing excessive noise in the result. An average of 26% of the 256 pixels are identified as 'noisy pixels' through two identification methods: i) For a homogenous background (e.g. in Fig. 2(b) where there is a region of only dark counts), the average dark count level is taken as a threshold and the data of all pixels above this threshold are removed. ii) For a non-homogenous background, for example with an underlying signal (e.g. if the time of travel through the fibre or a fluorescent decay exceeds the measurement period as discussed later), a moving average method is used. The moving average is calculated over a window size of 5 adjacent pixels. If the data of one pixel is greater than the average plus the standard deviation of this subset, it is removed. As seen in Figs. 2(b) and 2(d), a full data analysis from one measurement is enabled by slicing the data into three time windows along the histogram axis. The average background count level per pixel is derived from the dark count 'DC' time window shown in Fig. 2(b) and subtracted pixel-wise as detector pixels exhibit differing count rates. Note that in the case of a signal that exceeds the duration of the measurement period determined by the repetition rate, this time window contains not only detector background but also any other background signal such as fibre Raman or long lived fluorescence. The photon shot noise from these counts is still present in the final data. The 'fibre' time window contains the information about the backscattered fibre Raman spectral shape which can be used with a scaling factor to subtract the remaining fibre Raman signal from the 'fibre + SERS' time window (largely from the forward scattered fibre Raman) and thus the spectral information of MBA (as seen in Fig.  2(e)) can be recovered without a fibre background. Because of the uniformity of the fibre Raman, the time window can be placed anywhere along the fibre Raman signal. The scaling factor is needed to account for the reflection of the forward scattered fibre Raman on the multiple surfaces (fibre, NS, sol-gel). Figure 2(a) and 2(c) demonstrate that the time-resolved spectrometer, without applying the time windows, offers visually similar spectra to the commercial spectrometer with some important differences. The time-resolved spectrometer has a higher efficiency (producing larger overall signal amplitudes) but a lower spectral resolution leading to broadening and lower peak visibility for the SERS features at ~860 nm and ~900 nm compared to the commercial spectrometer. Meanwhile, the ratio of detector dark counts to signal is comparable between the reference measurement and the time-resolved spectrometer measurement (as shown in Figs. 2(a) and 2(c)). Through post-processing time-gating, the detector dark counts and the unwanted fibre Raman can be significantly suppressed and the visibility of the SERS Raman signal can be significantly increased (see Fig. 2(d)). For clearer observation of the Raman spectra, the measured fibre background (from the 'fibre' time window) is subtracted, demonstrating clear recovery of the true spectra from the fibre tip (see Fig. 2(e)).

Enhanced visibility of the Raman signal through post-processing time-gating
When time-gating the data the background counts are clearly reduced, thus reducing the background photon shot noise. For the purpose of this paper, we choose a time window of 5 time bins. This maximizes the signal-to-background (S/B) by removing the majority of the fibre background while additionally collecting the desired Raman signal over multiple time bins. However, increasing the time window width further than 5 time bins decreases S/B (see Appendix A.1.). For a fibre Raman dominant background, the S/B obtained was 4 × better in the time-gated result than that measured with the commercial spectrometer (integrated over the 857 nm peak). For a dark count dominated background, the S/B was 19 × better in the time-gated result than with the commercial spectrometer (897 nm peak), see Figs. 2(c) and 2(d).
These results could be improved if the instrument response function of the detector [23,24] and the pulse width of the laser were shorter (as discussed in Appendix A.1.), since the laser exhibits a long tail when operated at high power. The time-gating method in this paper is achieved by recording a whole TCSPC measurement and applying time windows to the data during post-processing. Others have presented time domain gating techniques such as streak cameras, electronically time-gated CCDs or CMOS detectors and optical driven Kerr gates [25]. While the latter achieves a time resolution of picoseconds, the setup is costly and measurement times lengthy (min). Electronic time-gating introduces additional jitter to the measurement through the enabling and disabling of the detector but potentially decreases the measurement time. However, we believe that time-gating in single photon counting (SPC) modality has no time advantage over TCSPC measurements in low light scenarios such as expected for in vivo sensing as measurement rate is limited by photon budget, not detector readout.
In biological applications, measurement of the SERS signal can be complicated further by fluorescence from delivered fluorophores or tissue autofluorescence which is always present. Figures 3(a)-3(c) shows how applying the time windows reduces the influence of the fluorescent background due to the differing time scales of Raman and fluorescence, demonstrating how the MBA spectrum can be successfully recovered. In Fig. 3(a) the spectrum is dominated by a large broad fluorescence response, successfully removed in Fig.  3(b), with a clear recovered spectrum in Fig. 3(c). For other applications, such as remote environmental sensing, longer fibre lengths are useful. In TCSPC methodology, the laser repetition rate determines the temporal duration of the measurement. The time of travel for the photons through the optical fibre can be calculated with t = (2nL)/c, where L is the fibre length, n is the refractive index of the fibre core material and c the speed of light in vacuum. Modal dispersion in multimode fibres can be expected to be in the order of tens of picoseconds per metre. We collect signal in a 2.1 ns time window, as such broadening through modal dispersion does not contribute to our measurements of 3 m or 18 m fibres, but if longer multimode fibres were used it would affect the S/B and a longer time window width would be required. If the repetition rate is shorter than the time of travel, photons are counted against the following sync signal and the measurement seems to be 'wrapped around' the histogram axis. In Figs. 3(d)-3(f) an 18 m optical fibre with functionalised gold NS deposited at the fibre tip was measured within a 50 ns measurement period. The excitation power was reduced to 0.12 mW to ensure a single photon counting regime and the integration time was increased to 60 s. The fibre Raman signal is 'wrapped' around 3.6 times, increasing the unwanted background, before the SERS signal is seen in the histogram. This means photons are arriving from subsequent laser pulses in the same TDC bin, due to insufficient delay between pulses. The MBA spectrum can be recovered but suffers from higher shot noise and the use of the lower excitation power decreases the signal from the NS. However, it is clear that the SERS peaks not visible in Fig. 3(d) have been recovered in Fig. 3(f). As an alternate to the data in Figs. 3(d)-3(f), the same fibre can be measured with a 5 MHz repetition rate ensuring the time of travel does not exceed the measurement period or the repetition rate of the laser. The expansion of the measurement period leads to a lower dark count level per time point (as DC are spread out over more time bins) but will increase the effect of the timing inhomogeneity of the CMOS SPADs [26], reducing the ability to accurately apply a narrow time window.
Additionally, to guarantee a single photon counting regime without pile-up [12], the average excitation power has to be decreased leading to both lower fibre Raman and SERS signal. If time is no constraint, a longer total measurement time compensates for the lower excitation power, and increases the accuracy of the measurement. However, for long fibres the combination of these factors results in a better recovered spectrum in the case of a short measurement period (high repetition rate) allowing the fibre background to wrap around, thus this method was chosen for the data shown here.

Application: pH sensing
The spectra of the MBA molecule is sensitive to environmental pH variations and has been previously demonstrated as a pH sensor [9,21]. Ratiometric changes of the areas under the curve (AUC), within a 4.75 nm spectral window, around the peaks of 880 nm (1380 cm −1 ) and 906 nm (1700 cm −1 ) respectively, show the greatest pH sensitivity. Figure 4 shows that time-gating the data greatly increases the selectivity and reduces the standard deviation of the mean over 3 replicates in comparison to a non time-resolved measurement. Increasing the integration time from 10 s (as shown in Fig. 4(a)) to 60 s (as shown in Fig. 4(b)) increases the accuracy of the system further and hence the selectivity.
The precision of the time-resolved spectrometer was evaluated by obtaining the AUC ratios for pH 6 and 8 for 50 consecutively acquired measurements. For a 10 s measurement a repeatability of 0.14 and 0.19 pH units, for pH 6 and 8 respectively, was achieved with timegating. For an integration time of 60 s this could be improved to 0.05 and 0.07 pH units, for pH 6 and 8 respectively. The precision of the pH sensor was determined by obtaining the AUC ratios while switching iteratively between pH 6 and 8 for 20 repeat measurements. For a 10 s measurement a repeatability of 0.25 and 0.30 pH units, for pH 6 and 8 respectively, was achieved with time-gating. Whilst, for an integration time of 60 s, this could be increased to 0.11 and 0.15 pH units, for pH 6 and 8 respectively. These results show that we are able to reach the same systematic stability which has been demonstrated earlier using the functionalised NS with a dual-core fibre and an adaptive iterative reweighted penalized least squares (airPLS) algorithm [10]. Decreased precision observed when switching between pH suggests some instability in the SERS sensors when moving repeatedly over large pH changes. The observed limits in measurement repeatability are larger than those expected from counting statistics after post-processing time-gating, and are instead believed to be due to detector fluctuation (varying pixel dark counts and photon detection probabilities), bias voltage fluctuations or thermal instabilities. Active temperature stabilisation as applied to commercial detectors could offer improved results. We also believe that cooling would greatly reduce the dark counts of the detector, reducing the shot noise and leading to better stability and accuracy. Improved timing accuracy and laser pulse width would offer further improved S/B.

Conclusion
A time-resolved system for recovering the spectra of weak Raman signals without fibre or fluorescent backgrounds has been demonstrated. pH sensing through a single core multimode optical fibre using short measurement times was achieved as an example of application. This methodology has high potential for ultra-miniaturized Raman probes for in vivo endoscopic sensing of physiological parameters such as pH, oxygen or glucose concentration as well as for remote environmental sensing. In terms of accuracy, the limit of the line sensor was reached and improvement has to include further detector calibrations such as photondetection variations and reduction of the dark counts through cooling. As time is crucial for in situ diagnosis scenarios, the already short integration time can be reduced further through onchip time-gating capabilities which has been demonstrated with this specific CMOS SPAD line sensor elsewhere [23].

A. 1. Signal-to-background investigation
where R N is the integrated number of counts in the area under the SERS peak at 857 nm, F N and DC N are the integrated number of counts in the same area of the Raman scattering of the fibre and the detector noise, respectively. The area under the peak was chosen as representative of the Raman signal strength, allowing direct comparison between spectrographs of differing resolution.