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Sensitivity of Transmission Raman Spectroscopy Signals to Temperature of Biological Tissues

Optical properties of biological tissues can be influenced by their temperature, thus affecting light transport inside the sample. This could potentially be exploited to deliver more photons inside large biological samples, when compared with experiments at room temperature, overcoming some of difficulties due to highly scattering nature of the tissue. Here we report a change in light transmitted inside biological tissue with temperature elevation from 20 to 40 °C, indicating a considerable enhancement of photons collected by the detector in transmission geometry. The measurement of Raman signals in porcine tissue samples, as large as 40 mm in thickness, indicates a considerable increase in signal ranging from 1.3 to 2 fold, subject to biological variability. The enhancements observed are ascribed to phase transitions of lipids in biological samples. This indicates that: 1) experiments performed on tissue at room temperature can lead to an underestimation of signals that would be obtained at depth in the body in vivo and 2) that experiments at room temperature could be modified to increase detection limits by elevating the temperature of the material of interest.

light needs to be delivered effectively into the tissues to depths of many tens of mm (or cm) and Raman molecular vibrational signals detected on the other side. The highly scattering nature of biological tissues makes light propagate in a random walk style, rather than directly (ballistic regime). This leads to a rapid loss of light from the optical axis, meaning only a fraction of the incident light is recovered typically from the other side of tissue. This approach is challenging due to difficulty of light delivery inside turbid media such as biological tissues; as well as the relative weakness of the Raman signal, combined with the high penetration depths required for breast screening (~40-50 mm).
Light propagation in tissue is principally governed by absorption and scattering being described by the coefficients (μ a ) and (μ s '), respectively 17 . If one minimises the effect of absorption inside tissue (e.g. by the appropriate choice of laser excitation wavelength) the scattering process can become the dominant factor contributing to light loss.
In previous work, we published the results of absorption measurements obtained using a modified advanced Transmission Raman setup optimized for detection of HAP inside 40 mm breast phantom tissue (pork). As a results of major instrumental improvements to yield enhanced light collection rates (x110 enhanced Raman photon acquisition rates 14 ) the desired sensitivity to detect small amounts of HAP and CO was achieved although this was still challenging within >40-50 mm thick tissues. Crucially, all the spectra reported in our previous paper were measured on phantoms at room temperature (~22 °C); this is significantly lower than the average biological temperature of human breast in vivo (~35 °C 18 ). Here we explore the dependence of TRS signals on temperature in this important temperature range.
The dynamics of optical properties of tissue associated with temperature represents a topic also of relevance to many biomedical applications such as low level laser therapy 19 . Applications which require light delivery deep inside the tissue for diagnostic purposes can also be affected. A few available papers addressing the temperature influence on the reduced scattering coefficient in biological samples point to a significant variation with temperature 20-23 observed, in a variety of biological tissue types, that can be correlated with structural adjustments in tissue heterogeneity. At temperatures where protein denaturation occurs a sharp change in scattering coefficient has been reported 24 . It should be noted that all our experiments were performed below 40 °C to avoid any irreversible biochemical processes in tissue.
This paper explores the changes in relative transparency of biological tissues, from the standpoint of transmission Raman spectroscopy (TRS), with temperature. Specifically, when going from room temperature to natural body temperature. To date, the main body of research carried out on excised biological tissues has focused predominantly on studies at room, or lower temperatures. Although some studies did report significant dependence of phantom tissue optical properties on temperature, indicating significant changes in the μ s 19,25-28 value with elevated temperatures and approximate invariance of μ a to temperature the influence of these effects on TRS signals, which involves photon transport of both laser photons as well as inelastically scattered photons, has not been reported to date. It is therefore important to assess the role of temperature in the context of such studies. Here we present preliminary results obtained using a Transmission Raman platform on samples placed in a thermal bath. The Raman spectra were recorded at several temperatures and the results were analysed to assess the influence of temperature on the retrieved TRS signal. The phenomena reported here is not limited to TRS of biological samples. In fact it may play a role also when performing conventional backscattering Raman spectroscopy or imaging of biological tissues.

Materials and Methods
Sample preparation. The breast tissue phantoms used in this study were made of porcine shoulder tissues.
These contained skin, fat and muscle replicating crudely much of the gross chemical composition of human breast tissue. The tissue samples were purchased fresh from a local supermarket and sliced to a thickness of around 40 mm (illumination path-length) × 35 mm × 50 mm (precision of ±1.5 mm) to fit inside a quartz container. The samples were wrapped in a fine polyethylene cling film to avoid water evaporation during experiments.
Two different amounts of calcium hydroxyapatite (HAP) powder (Sigma Aldrich, St Louise, USA), representing type II breast calcifications 29 , 80 mg and 120 mg were smeared on tissue in the middle of sample over a disk shape area (of approximately 4 mm diameter) oriented perpendicularly to the optical axis.
A thermal water bath was used to control sample temperature. The water was piped to a copper based heat exchange element placed underneath, on the left and on right of the sample (see Fig. 1) permitting a uniform and steady heating of samples to desired temperatures.
Transmission Raman Instrument. The schematic of the TRS setup is presented in Fig. 1 with a detailed description given in our earlier paper 30 . The laser used in these experiments was a solid state laser operating at 808 nm (Innovative Photonic Solutions, Monmouth Junction, NJ, US) and the light was delivered to the sample using an optical fibre (550 µm diameter, 0.22 N.A., Thorlabs, USA). Prior to spectral filtering the laser output was expanded and collimated to 6-8 mm diameter using a biconvex lens with 25 mm focal length and 25 mm diameter. The Raman signal was collected on the other side of the sample with a 50 mm diameter biconvex collection lens of 38 mm focal length (N.A. = 0.6) which directed the light towards relaying lens of the same diameter and a focal length of 60 mm to deliver the light inside spectrometer. A couple of long pass edge filters at 830 nm (LP02-830RU-25, Semrock, Rochester, US) were deployed to filter out (O.D. 7) the elastically scattered light, first being placed between collection and focusing lens and the second located inside the spectrometer. The spectrometer employed in the setup, Holospec 1.8i (Kaiser Optical Systems, Ann Arbor, Michigan, USA) was equipped with a high dispersion grating covering a spectral range of 608-1243 cm −1 . A deep depletion CCD detector, Andor iDus 420 (Andor, Belfast, UK) was coupled with the spectrometer to collect the Raman signals. The slit used inside the spectrometer was 1 mm wide, which, combined with a high resolution diffraction grating, provided a spectral resolution of ∼15 cm −1 . Some additional measurements of tissue chemical evolution with temperature were Temperature monitoring. Temperature monitoring was performed using a Thermocouple Data Logger (Pico Technology, Cambridgeshire, UK) via 4 channels using probes located in the thermal bath, the quartz vial outside the tissue and inside the tissue. Data analysis. All the recorded spectra were imported into Matlab for data pre-processing, which consisted of cosmic background removal, noise filtering using singular value decomposition, background subtraction (first order polynomial) and detector intensity offset removal. Additional peak fitting of the Raman bands intensities were performed using Gaussian peak fitting in Origin (OriginLab, Northampton, USA) following a first order polynomial baseline subtraction.

Results and discussions
Tissue attenuation profile. Figure 2 presents the evolution of the transmission profiles of porcine tissue, with 120 mg HAP powder samples located within the tissue, in the temperature range of 20-40 °C. The blue and red lines mark laser excitation wavelength and corresponding Raman peak of HAP (~960 cm −1 ), respectively. The data provides a direct indication of temperature spectral effects at both the laser and Raman wavelengths. It is evident that more laser photons can travel deeper into tissue and the Raman (signal) photons more easily escape as a result of the overall increase of transparency at elevated temperatures. Thus by increasing tissue temperature from room to human body temperature, one would expect to observe a higher level of TRS signal leading to consequential higher detection sensitivity.
The observed spectra are dominated by the absorption peaks of fat and water 17 . As the temperature of the tissue is elevated from 20 to 30 °C, we observe a ~30% increase in transmission at the relevant wavelengths. A less significant increase is observed by further elevation to 37 °C/40 °C. This behaviour is likely to be related to the melting of numerous lipids at various temperature points and associate change of their scattering properties 31,32 . Porcine adipose tissue exhibits a heat induced change around 26 °C and 35 °C 32 . Subcutaneous fats have phase changes between 26 °C and 47 °C 32 with the most significant around 31 °C.
All the transmission measurements of tissue with inclusions of either 120 mg or 80 mg HAP indicate a broadly consistent evolution of the peak heights with temperature for each HAP amount with insignificant influence of HAP powder presence (supporting information Fig. S1b). This is consistent with the fact that the tiny amounts of HAP would not be expected to affect the measured transmission profiles to any significant degree. This is also confirmed through similar data obtained from tissue alone (Fig. S2b). Temperature dependence of TRS of porcine tissue. As anticipated the TRS measurements carried out on 40 mm-thick porcine tissue at different temperatures reveal a significant enhancement of TRS signals at elevated temperatures from 20 to 40 °C, a type of behaviour not reported previously (Fig. 3). The Raman spectral evolution with temperature is consistent with literature data on tissue absorption profile changes with temperature, as well as our above findings, evidencing increased light transmission through thick biological tissue at both the laser excitation and Raman wavelengths with elevated temperatures above the room temperature.
Interestingly, we have also observed the presence of a small Raman band (marked with red highlighted strip) around 1120 cm −1 at 20° C, which disappears at higher temperature. The band has been observed consistently in other porcine samples measured under similar conditions. Because of the lower spectral resolution and narrower spectral coverage, we have also performed additional temperature dependence experiments using a low dispersion grating and 50 microns slit on adipose tissue. Figure 4 confirms the presence of the same band at low temperatures and its disappearance at higher temperatures. The data also evidences a shift of the band from ~1060 cm −1 (19 °C) to ~1070 cm −1 (35 °C). Overall, we observe tissue Raman bands which are typically present at ambient temperature: 883 cm −1 -red arrow, 1119 cm −1 -pink arrow corresponding to C-C stretching of oleic acid and triglycerides 33 , 1062 cm −1 -blue arrow, and 1175 cm −1 -arrow of palmitic acids saturated fat 33 . Porcine adipose tissue contains a high percentage of polyunsaturated fat 34 , since several peaks associated with oleic acids are present. As the temperature increases a band shift from 1062 cm −1 -blue arrow (C-C aliphatic out-of-phase stretch of triglycerides 35 ) towards  1073 cm −1 -green arrow while the rest of the bands mentioned above, completely vanish over 30 °C indicating a change in structure of the lipids from gel to liquid configuration. A zoom into the spectral region of 800 cm −1 -1100 cm −1 is presented in Fig. S3; the entire spectral region exhibits an increase in intensity with increasing temperature. We were unable to ascertain whether Raman signal from lipids was higher or lower in absolute terms.
We tested our hypothesis of improved sensitivity of TRS detection of calcifications in samples at elevated temperatures within a 40 mm thick porcine sample containing 120 mg HAP at its centre. To visualise the weak HAP band we subtracted the TRS signal obtained with tissue alone from that measured with HAP 120 mg within it. The HAP was contained within a quartz vial. The cell was placed inside the tissue in its centre and kept at the same position throughout the measurements. The HAP powder was wrapped in 'cling film' and inserted in the cell without disturbing surrounding tissue; thus ensuring a high reproducibility between measurements. Difference spectra plotted in a spectral region around the 960 cm −1 HAP band are presented in Fig. 5a. The observed differences evidence the expected evolution of the HAP peak in tissue with temperature. As expected, the biggest jump in HAP Raman intensity is observed between 20 °C and 30 °C. Further elevation from 30 to 40 °C appears to have much smaller influence on the HAP band intensity. The overlap of two difference spectra obtained at 40 °C and 20 °C in Fig. 5b shows more clearly the enhancement of the HAP band intensity with increased temperature. The peak analysis using Gaussian peak fitting yielded a two-fold increase in the peak area between the two temperature points.  The measurements were repeated on other tissue samples (example in Fig. S2). The spectra appear to be noisier, as the changes in peak height/area were less pronounced, an indication of a more scattering sample and explained by tissue variability between two different batches of porcine meat. Overlap of spectral differences at the same temperatures 20 °C and 40 °C are consistent with the results derived from the first sample although the band profiles are less distinguishable due to lower SNR. The estimated gain in TRS signal intensity in this sample was around 30%.
In conclusion we described the effect of temperature on TRS signal strength within both the tissue matrix and any inclusions buried within it. The temperatures explored ranged from room to normal body temperatures (35-37 °C). The smallest recorded value of the TRS signal enhancement in 40 mm thick porcine tissue samples was 30%. The changes are ascribed to temperature specific phase transitions of glycolipids and a consequential reduction of the overall tissue scattering coefficient.