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Virtual Journal for Biomedical Optics

Virtual Journal for Biomedical Optics

| EXPLORING THE INTERFACE OF LIGHT AND BIOMEDICINE

  • Editors: Andrew Dunn and Anthony Durkin
  • Vol. 9, Iss. 5 — Apr. 29, 2014
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Correction of optical absorption and scattering variations in laser speckle rheology measurements

Zeinab Hajjarian and Seemantini K. Nadkarni  »View Author Affiliations


Optics Express, Vol. 22, Issue 6, pp. 6349-6361 (2014)
http://dx.doi.org/10.1364/OE.22.006349


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Abstract

Laser Speckle Rheology (LSR) is an optical technique to evaluate the viscoelastic properties by analyzing the temporal fluctuations of backscattered speckle patterns. Variations of optical absorption and reduced scattering coefficients further modulate speckle fluctuations, posing a critical challenge for quantitative evaluation of viscoelasticity. We compare and contrast two different approaches applicable for correcting and isolating the collective influence of absorption and scattering, to accurately measure mechanical properties. Our results indicate that the numerical approach of Monte-Carlo ray tracing (MCRT) reliably compensates for any arbitrary optical variations. When scattering dominates absorption, yet absorption is non-negligible, diffusing wave spectroscopy (DWS) formalisms perform similar to MCRT, superseding other analytical compensation approaches such as Telegrapher equation. The computational convenience of DWS greatly simplifies the extraction of viscoelastic properties from LSR measurements in a number of chemical, industrial, and biomedical applications.

© 2014 Optical Society of America

1. Introduction

The primary challenge in extracting the viscoelastic modulus of turbid and absorbing samples from speckle frame series lies in evaluating the MSD from the measured g2(t) curve. This is because the rate of temporal speckle fluctuations depends not only on the Brownian displacement of scattering centers, but also on the optical properties, such as absorption and reduced scattering coefficients (μa, μs'), that determine the transport of light within the illuminated volume [11

11. Z. Hajjarian and S. K. Nadkarni, “Evaluation and Correction for Optical Scattering Variations in Laser Speckle Rheology of Biological Fluids,” PLoS ONE 8(5), e65014 (2013). [CrossRef] [PubMed]

, 20

20. D. A. Boas and A. G. Yodh, “Spatially varying dynamical properties of turbid media probed with diffusing temporal light correlation,” J. Opt. Soc. Am. A 14(1), 192–215 (1997). [CrossRef]

22

22. A. Mazhar, D. J. Cuccia, T. B. Rice, S. A. Carp, A. J. Durkin, D. A. Boas, B. Choi, and B. J. Tromberg, “Laser speckle imaging in the spatial frequency domain,” Biomed. Opt. Express 2(6), 1553–1563 (2011). [CrossRef] [PubMed]

]. Therefore, in order to accurately measure sample mechanical properties using LSR, it is critical to isolate the influence of optical absorption and scattering from the g2(t) measurements to accurately describe the MSD.

2. Materials and methods

2.1 Preparing test phantoms of varying optical properties

The studies reported here were performed using solutions of 90% glycerol and 10% water, with identical viscosity values of η ~0.24 Pa. s (at 20° C). The optical properties of liquid phantoms were tuned by adding various concentrations of TiO2 scattering particles (dia. 400 nm, Sigma-Aldrich) and carbon light absorbing nano-powder (dia. 423 nm, Sigma-Aldrich), such that the reduced scattering and absorption coefficients ranged from: µs' = 1.2 - 129.2 mm−1 and µa = 0.14-9.95 mm−1 (@ 633 nm). These included the optical properties relevant to biological tissue, such as blood, with low µs' (1-4 mm−1) within the visible and infrared spectrum [26

26. T. B. Rice, S. D. Konecky, A. Mazhar, D. J. Cuccia, A. J. Durkin, B. Choi, and B. J. Tromberg, “Quantitative determination of dynamical properties using coherent spatial frequency domain imaging,” J. Opt. Soc. Am. A 28(10), 2108–2114 (2011). [CrossRef] [PubMed]

, 27

27. S. T. Flock, S. L. Jacques, B. C. Wilson, W. M. Star, and M. J. van Gemert, “Optical properties of Intralipid: a phantom medium for light propagation studies,” Lasers Surg. Med. 12(5), 510–519 (1992). [CrossRef] [PubMed]

], dairy products and common industrial coating and films with medium µs' values (4-30 mm−1) [28

28. W. R. Calhoun, H. Maeta, S. Roy, L. M. Bali, and S. Bali, “Sensitive real-time measurement of the refractive index and attenuation coefficient of milk and milk-cream mixtures,” J. Dairy Sci. 93(8), 3497–3504 (2010). [CrossRef] [PubMed]

, 29

29. G. Latour, M. Elias, and J.-M. Frigerio, “Determination of the Absorption and Scattering Coefficients of Pigments: Application to the Identification of the Components of Pigment Mixtures,” Appl. Spectrosc. 63(6), 604–610 (2009). [CrossRef] [PubMed]

], and rich scattering material (µs'> 30 mm−1) in which light propagation could conveniently assumed to be diffusive. The glycerol suspensions were mixed in a vortex to evenly distribute particles within the final suspension, and transferred into disposable spectroscopic cuvettes (Fischer brand, light path 10 mm, vol. 1.5 ml) for LSR measurements. In all cases, Mie theory was used to calculate the optical properties of the samples and the sizes of TiO2 and carbon particles were confirmed using a dynamic light scattering instrument (Zetasizer, Malvern Instruments Ltd., UK) [23

23. L. V. Wang and H. Wu, Biomedical optics: principles and imaging (Wiley-Interscience, 2007).

]. Choice of water-glycerol mixtures of the same viscosity (η ~0.24 Pa) and TiO2 and carbon particles of almost identical sizes ensured that all samples were mechanically similar and had indistinguishable Brownian dynamics. Thus, any observed variability in speckle fluctuations rate was solely due to optical property differences.

2.2 Laser speckle rheology: image acquisition and analysis

Time-varying speckle images of the prepared samples were acquired using the optical setup shown in Fig. 1
Fig. 1 LSR Instrumentation [10]. Laser beam was passed through a polarizer (P), a beam expander (BE), and focused on the sample by a lens (L1). The backscattered light was redirected by a beam-splitter (BS) towards the camera aperture and passed through a polarizer (P). The cross polarized light was then focused by a lens (L2) at the CMOS sensor.
and fully described in our earlier work [6

6. S. K. Nadkarni, B. E. Bouma, T. Helg, R. Chan, E. Halpern, A. Chau, M. S. Minsky, J. T. Motz, S. L. Houser, and G. J. Tearney, “Characterization of atherosclerotic plaques by laser speckle imaging,” Circulation 112(6), 885–892 (2005). [CrossRef] [PubMed]

, 7

7. S. K. Nadkarni, A. Bilenca, B. E. Bouma, and G. J. Tearney, “Measurement of fibrous cap thickness in atherosclerotic plaques by spatiotemporal analysis of laser speckle images,” J. Biomed. Opt. 11(2), 021006 (2006). [CrossRef] [PubMed]

, 9

9. Z. Hajjarian, J. Xi, F. A. Jaffer, G. J. Tearney, and S. K. Nadkarni, “Intravascular laser speckle imaging catheter for the mechanical evaluation of the arterial wall,” J. Biomed. Opt. 16(2), 026005 (2011). [CrossRef] [PubMed]

, 10

10. Z. Hajjarian and S. K. Nadkarni, “Evaluating the viscoelastic properties of tissue from laser speckle fluctuations,” Sci. Rep. 2, 316 (2012). [CrossRef] [PubMed]

]. Briefly, a Helium-Neon laser beam (633nm, 21 mW) was polarized, expanded, and focused to a 50 µm spot. The power on the sample was 4.5 mW. Cross-polarized laser-speckle patterns were acquired at 180° backscattering geometry using a high frame rate CMOS camera (Basler Ace, acA 2000-340 km) and a frame grabber (NI PCIe-1433 Camera Link) for 2 seconds at 964 frames per second (fps) (exposure time <600 μs). Such a high frame rate, allowed calculating the speckle intensity autocorrelation function, g2(t), with sufficient temporal resolution with approximately 1000 time-varying speckle images acquired between the start point (t = 0s) up to the plateau level (t ~1s). In addition, the camera aperture was set to maintain a pixel to speckle ratio of at least 4 to ascertain sufficient spatial sampling and spatial speckle contrast. The resulting camera field of view (FOV) was 2 mm, with the illumination spot located in the center of the FOV. These adjustments raised the contrasts of speckle frame series up to the maximum value of 1. The speckle intensity temporal autocorrelation curve, g2(t), was calculated by measuring the correlation between pixel intensities in the first speckle image and subsequent images. Spatial averaging was performed over all 280 × 280 pixels in the frame, and 500 g2(t) curves evolving in time were averaged to enhance the accuracy of temporal statistics as follows [6

6. S. K. Nadkarni, B. E. Bouma, T. Helg, R. Chan, E. Halpern, A. Chau, M. S. Minsky, J. T. Motz, S. L. Houser, and G. J. Tearney, “Characterization of atherosclerotic plaques by laser speckle imaging,” Circulation 112(6), 885–892 (2005). [CrossRef] [PubMed]

11

11. Z. Hajjarian and S. K. Nadkarni, “Evaluation and Correction for Optical Scattering Variations in Laser Speckle Rheology of Biological Fluids,” PLoS ONE 8(5), e65014 (2013). [CrossRef] [PubMed]

]:
g2exp(t)=I(t0)I(t0+t)pixelsI(t0)2pixelsI(t0+t)2pixelst0.
(1)
Here I(t0) and I(t + t0) refer to the speckle intensity at times t0 and t + t0, < >pixels and < >t0 indicate spatial and temporal averaging over all the pixels in the images and for the entire imaging duration (2s), respectively.

2.3 Extracting the MSD and viscoelastic modulus, |G*(ω)|, from g2(t) curves

We have recently derived an alternative numerical approach to describe the g2(t) and MSD relationship, by implementing a polarization-sensitive correlation transfer PSCT-MCRT algorithm which provides a more precise account of light propagation in turbid materials [11

11. Z. Hajjarian and S. K. Nadkarni, “Evaluation and Correction for Optical Scattering Variations in Laser Speckle Rheology of Biological Fluids,” PLoS ONE 8(5), e65014 (2013). [CrossRef] [PubMed]

]. In short, the PSCT-MCRT approach incorporates the illumination/collection setup, sample geometry, polarization state, absorption and scattering coefficients, (µa, µs) and anisotropy factor, g, to track the scattering wave vector, defined as q = 2k0sin(θ/2), at each photon-particle collision event [11

11. Z. Hajjarian and S. K. Nadkarni, “Evaluation and Correction for Optical Scattering Variations in Laser Speckle Rheology of Biological Fluids,” PLoS ONE 8(5), e65014 (2013). [CrossRef] [PubMed]

, 25

25. S. Sakadzić and L. V. Wang, “Correlation transfer equation for multiply scattered light modulated by an ultrasonic pulse,” J. Opt. Soc. Am. A 24(9), 2797–2806 (2007). [CrossRef] [PubMed]

]. Here θ is the polar angle of scattering. Compared to the path length distribution, P(S), exploited in DWS, the total momentum transfer distribution, P(Y) (Y = ∑q2/(2k02)), obtained from MCRT simulations, is expected to provide a superior description of correlation decay of each path [30

30. D. J. Durian, “Accuracy of diffusing-wave spectroscopy theories,” Phys. Rev. E Stat. Phys. Plasmas Fluids Relat. Interdiscip. Topics 51(4), 3350–3358 (1995). [CrossRef] [PubMed]

]. A mathematically tractable solution is obtained by curve-fitting techniques, which yield the following expression for g2(t) [11

11. Z. Hajjarian and S. K. Nadkarni, “Evaluation and Correction for Optical Scattering Variations in Laser Speckle Rheology of Biological Fluids,” PLoS ONE 8(5), e65014 (2013). [CrossRef] [PubMed]

]:
g2MCRT(t)=e2γ(k02n2Δr2(t))ζ
(3)
For a fixed choice of illumination/collection setup and sample geometry, the parameters γ and ζ in Eq. (3) depend only on the optical properties, namely μa and μs' = μs(1-g). While our prior work focused on the purely scattering samples [11

11. Z. Hajjarian and S. K. Nadkarni, “Evaluation and Correction for Optical Scattering Variations in Laser Speckle Rheology of Biological Fluids,” PLoS ONE 8(5), e65014 (2013). [CrossRef] [PubMed]

], here, we executed the PSCT-MCRT code and calculated the (γ, ζ) pairs for µs' = 1.2-129.2 mm−1 and µa = 0.14-9.95 mm−1.

In this study, we investigated the performance of DWS and PSCT-MCRT in deducing the MSD from speckle intensity fluctuations by replacing g2exp(t) in the corresponding equations (Eqs. (2) and (3)). The MSD values were then substituted in the well-established generalized Stokes-Einstein relation (GSER) to calculate the |G*(ω)| [14

14. T. G. Mason and D. A. Weitz, “Optical measurements of frequency-dependent linear viscoelastic moduli of complex fluids,” Phys. Rev. Lett. 74(7), 1250–1253 (1995). [CrossRef] [PubMed]

19

19. M. Jonas, H. Huang, R. D. Kamm, and P. T. So, “Fast fluorescence laser tracking microrheometry. I: instrument development,” Biophys. J. 94(4), 1459–1469 (2008). [CrossRef] [PubMed]

]:
G*(ω)=KBTπaΔr2(t)Γ(1+α(t))|t=1/ω
(4)
Here KB is the Boltzman constant (1.38 × 10−23), T = 297 (room temperature) is the absolute temperature (degrees Kelvin), a~200 nm is the particle radius (based on the product specifications and independent DLS particle sizing), ω = 1/t is the loading frequency, Γ represents the gamma function, and α(t) = ∂ log <Δr2(t)>/ ∂ log t corresponds to logarithmic derivative of MSD. The GSER approximation used to estimate the G*(ω) from the MSD is well documented by others in the past [14

14. T. G. Mason and D. A. Weitz, “Optical measurements of frequency-dependent linear viscoelastic moduli of complex fluids,” Phys. Rev. Lett. 74(7), 1250–1253 (1995). [CrossRef] [PubMed]

19

19. M. Jonas, H. Huang, R. D. Kamm, and P. T. So, “Fast fluorescence laser tracking microrheometry. I: instrument development,” Biophys. J. 94(4), 1459–1469 (2008). [CrossRef] [PubMed]

]. The glycerol phantoms, studied here, were purely viscous and homogeneous. Since this criterion for the validity of GSER was met, |G*(ω)| could be directly drawn from the MSD [14

14. T. G. Mason and D. A. Weitz, “Optical measurements of frequency-dependent linear viscoelastic moduli of complex fluids,” Phys. Rev. Lett. 74(7), 1250–1253 (1995). [CrossRef] [PubMed]

19

19. M. Jonas, H. Huang, R. D. Kamm, and P. T. So, “Fast fluorescence laser tracking microrheometry. I: instrument development,” Biophys. J. 94(4), 1459–1469 (2008). [CrossRef] [PubMed]

].

2.4 Comparing the accuracy of LSR results with conventional mechanical testing

The performance of DWS and MCRT approaches in deriving the MSD and |G*(ω)| from LSR measurements was compared with reference standard mechanical rheometry (AR-G2, TA Instruments, MA) for all phantoms. Each sample (2 ml) was placed on a stationary temperature controlled peltier plate and a top plate of 40 mm diameter sheared the sample at oscillation frequencies of 0.1-100 Hz at 2% strain to obtain the frequency dependent viscoelastic modulus, G*(ω). Mechanical testing was carried out at 25°C.

3. Results

3.1 The influence of scattering properties on speckle intensity fluctuations

Next, we report the performances of DWS and PSCT-MCRT, in isolating the influence of scattering properties on the G*(ω) evaluated by the LSR. For this analysis, the MSD is deduced from the experimentally evaluated g2(t) curves of Fig. 2, using each of Eqs. (2), and (3), and substituted in Eq. (4) to calculate the frequency-dependent viscoelastic modulus |G*(ω)| displayed in Fig. 3
Fig. 3 Viscoelastic modului, |G*(ω)|, extracted from g2(t) curves of Fig. 2, using (a) DWS equation, and (b) PSCT-MCRT based approach. The viscoelastic modulus measured using a conventional rheometer is shown as a black dashed curve. For these primarily scattering samples of negligible absorption, DWS fails to yield an accurate estimate of viscoelastic properties. In contrast, PSCT-MCRT successfully derives the moduli from g2(t) curves of Fig. 2.
. Standard mechanical rheometry measurement is also conducted and the results are displayed for comparison with the LSR measurements as a dashed black curve. Clearly, |G*(ω)| curves obtained via DWS formalism in Fig. 3(a) present a considerable deviation from conventional rheology. The failure in accurate extraction of |G*(ω)|, is drastically aggravated for biologically relevant μs' values (1-3 mm−1). In this range, relatively slower speckle fluctuations, generated by a smaller number of light scattering events, erroneously result in an over-estimation of the |G*(ω)|. It is only for µs' = 129.2 mm−1 that the LSR measurements, derived by DWS (Fig. 3(a)) converge to the results of mechanical rheometry.

On the contrary, the PSCT-MCRT approach succeeds in sufficiently isolating optical scattering contributions to estimate moduli for any arbitrary μs' value (Fig. 3(b)). The measured |G*(ω)| curves corresponding to weakly, moderately, and strongly scattering samples show close correspondence with the results of conventional rheology, especially at intermediate frequencies. At low and high frequency limits, a small deviation of |G*(ω)| curves is observed between LSR and mechanical rheometry potentially caused by speckle contrast artifacts and rheometer inertia limitations, respectively, as discussed later [10

10. Z. Hajjarian and S. K. Nadkarni, “Evaluating the viscoelastic properties of tissue from laser speckle fluctuations,” Sci. Rep. 2, 316 (2012). [CrossRef] [PubMed]

, 11

11. Z. Hajjarian and S. K. Nadkarni, “Evaluation and Correction for Optical Scattering Variations in Laser Speckle Rheology of Biological Fluids,” PLoS ONE 8(5), e65014 (2013). [CrossRef] [PubMed]

].

3.2 The influence of absorption properties on speckle intensity fluctuations

The results presented in this section are obtained by varying optical absorption while scattering properties are kept constant. Figure 4
Fig. 4 Speckle intensity temporal autocorrelation curves for aqueous glycerol suspensions of varying absorption coefficient. As μa increases, speckle fluctuations decelerate, and g2(t) curves decay slower.
displays g2(t) curves of samples with identical viscosities and µs' ~2.4, with µa: 0 – 0.54 mm−1. Clearly, variation of absorption properties greatly influences the g2(t) curve. When µa increases, temporal speckle intensity fluctuations slow down, likely due to elimination of longer optical paths, which involve a larger number of scattering events. Clipping of these paths, rounds off the rapid initial decay of g2(t) curve [1

1. D. A. Weitz and D. J. Pine, “Diffusing-Wave Spectroscopy,” in Dynamic Light Scattering: The Methods and Some Applications, W. Brown, ed. (Oxford University, 1993) (49).

]. However, the impact of absorption on the long time behavior is rather small. This part of the curves is primarily modulated by shorter optical paths that are less influenced by absorption and encountered less number of scattering events [1

1. D. A. Weitz and D. J. Pine, “Diffusing-Wave Spectroscopy,” in Dynamic Light Scattering: The Methods and Some Applications, W. Brown, ed. (Oxford University, 1993) (49).

]. As a result, when µa increases, the curvature and the trend of g2(t) at early times are modified.

Figure 5
Fig. 5 Viscoelastic modulus, |G*(ω)|, obtained from g2(t) curves of Fig. 3, using (a) DWS equation, and (b) PSCT-MCRT for glycerol suspensions of identical mechanical properties, similar reduced scattering coefficient, μs', but varying absorption coefficient, μa. The viscoelastic modulus measured using a conventional rheometer is shown as a dashed black curve. It is clear that DWS is capable of correcting for the influence of variations in μa. PSCT- MCRT performs well for any arbitrary set of optical properties.
displays the resulting |G*(ω)|, obtained from g2(t) curves of Fig. 4, as described above. In contrast to Fig. 3(a), which clearly displays the errors induced in estimated |G*(ω)| values by scattering variations, it appears that DWS is fairly resilient to absorption-induced adjustment of speckle intensity fluctuations, whenever μa is non-negligible. The capability of DWS in extracting the MSD and consequently the |G*(ω)|, in the presence of non-negligible absorption is noted in Eq. (2). This equation incorporates the influence of absorption in the term μa/μs', and predicts that for a fixed μs', an increase in μa, leads to slower speckle fluctuations, which is consistent with the experimental results of Fig. 4. Nonetheless, in the purely scattering sample, with μs' = 2.5 and μa = 0, the term μa/μs' reduces to 0 and |G*(ω)| values derived using DWS formalism exhibit a significant deviation from the rheology measurements. Moreover, in samples μa/μs' > 0.1, changes in the curvature of g2(t) curve, observed in Fig. 4, induces a slight deviation at intermediate frequencies as discussed later. In Fig. 5(b), |G*(ω)| curves derived via PSCT-MCRT approach are displayed. As expected, PSCT-MCRT effectively compensates for the attributes of absorption variation from the final |G*(ω)| curves in all cases. Just as in Fig. 3, small deviations are still present at low/high frequency limits due to experimental artifacts.

3.3 The combined influence of scattering and absorption on speckle intensity fluctuations

In the above sections thus far, we have separately investigated the influence of scattering and absorption variations on speckle intensity fluctuations, by keeping one of the μs' and μa fixed, and modifying the other. To obtain the results in Fig. 6
Fig. 6 Speckle intensity temporal autocorrelation curve, g2(t) for samples of varying μs' and μa. In panel (a) samples with higher μs' have a smaller μa, whereas in panel (b) μs' and μa are proportional.
, both μs' and μa are varied simultaneously. At first, in Fig. 6(a), we consider the influence of increasing the μa while reducing the μs' (μa↑, μs'↓) on the speckle fluctuations. In the second scenario, in Fig. 6(b), speckle fluctuations are modified by increasing both μs' and μa (μs' ↑, μa↑).

In Fig. 6(a), the differences of (μs', μa) pairs cause a significant variation in the experimentally measured g2(t). For the moderately scattering sample of negligible absorption (μs' ~13 mm−1 and μa ~0), light scatters multiple times before being detected and minute displacements of scattering particles, involved in each optical path, accumulate and induce a rapidly decaying g2(t) curve. By gradually adding small amounts of absorbing particles and reducing the scattering concentration, (for instance in samples with μ's = 6.1 mm−1, μa = 0.14 mm−1; μs' = 4.9 mm−1, μa = 0.27 mm−1, μs' = 3.7 mm−1, μa = 0.41 mm−1, and μs' = 2.4, μa = 0.54 mm−1), long optical paths are ultimately absorbed and g2(t) curves slow down, proportionally. Notice that for these curves, μa/μs' values are equal to 0.0022, 0.055, 0.11, and 0.23 respectively. Thus, as the exponent in Eq. (2) predicts, by gradual growth of μa/μs' ratio, g2(t) proportionately slows down. In one case, for the most weakly scattering samples of strong absorption, (μs' = 1.2 mm−1, μa = 0.68 mm−1), the rays scatter only a few times, due to the sparse distribution of scattering centers. Besides, strong absorption extensively eliminates long optical paths that propagate through the medium. Therefore, the initial decay of g2(t) slows down significantly, and as observed in Fig. 6(a), leading to a drastic modification of the g2(t) curvature at the intermediate times. For this phantom, the μa/μs' ratio rises to 0.49, indicating that μs' are μa comparable and the underlying assumption of DWS, i.e. μa << μs', is at the verge of breakdown.

As opposed to Fig. 6(a), in Fig. 6(b) g2(t) curves follow a very similar decay trend, despite considerable difference in optical properties. In this panel, optical properties of samples are chosen so that μs' and μa vary almost proportionally. Increasing μs' is expected to increase the number of received long optical paths of faster decorrelation. However, simultaneous increase of μa trims these paths and cancels out the influence of larger μs'. Thus, by simultaneously increasing both μs' and μa speckle fluctuations rates vary minimally, which is reflected by the small variability of μa/μs': 0.08 - 0.1, ensuing only minute shifts in the g2(t) curves.

Figures 7(a)
Fig. 7 Viscoelastic modulus, |G*(ω)|, obtained from g2(t) curves of Fig. 6(a), using (a) DWS equation, and (b) PSCT-MCRT, for glycerol suspensions of identical mechanical properties and varying μ's and μa. The viscoelastic modulus measured using a conventional rheometer is shown as a black dashed curve. |G*(ω)| derived from speckle fluctuations, exhibit close agreement with conventional rheology, except when μ's = 1.2 and μa = 0.68.
, and 7(b) display the resulting viscoelastic moduli, extracted from g2(t) curves of Fig. 6(a), using DWS and PSCT-MCRT simulations, respectively. Clearly, viscoelastic moduli corresponding to samples of low to moderate μa represent close agreement with the results of conventional rheology in both cases (Fig. 7(a) and 7(b)). Only in one case, where μs' is the lowest and the μa is the highest (μs' = 1.2, μa = 0.68 mm−1) the irregular g2(t) curvature leads to a slight deviation of the LSR results from mechanical rheometry at intermediate frequencies, especially in the case of DWS.

Figure 8
Fig. 8 Viscoelastic modulus, |G*(ω)|, obtained from g2(t) curves of Fig. 6(b) using (a) DWS equation, and (b) PSCT-MCRT. The viscoelastic modulus measured using a conventional rheometer is shown as a black dashed curve. In both cases, modulus values match the results of conventional rheometry.
displays the results of |G*(ω)|, obtained from g2(t) curves of Fig. 6(b), using DWS equation (Fig. 8(a)), and PSCT-MCRT (Fig. 8(b)). Both approaches can successfully isolate the contribution of optical properties in samples, for which μs' and μa are non-negligible and proportional, as shown in Fig. 8(a) and 8(b). It is worth noting that the optical properties of blood at 690 nm are very close to the phantom with μs' = 1.2 mm−1 and μa = 0.14 mm−1 [31

31. V. V. Tuchin, Handbook of optical biomedical diagnostics (SPIE Press, 2002).

]. Since DWS and MCRT behave the same in this case, they may accurately and effectively evaluate the viscoelastic properties of the blood, in its native state, from laser speckle fluctuations.

4. Discussion

We have previously established the close correspondence between the temporal trend of the g2(t) curve and mechanical properties over a wide range of viscoelastic moduli in phantoms, excised tissue, and living animals, in vivo [9

9. Z. Hajjarian, J. Xi, F. A. Jaffer, G. J. Tearney, and S. K. Nadkarni, “Intravascular laser speckle imaging catheter for the mechanical evaluation of the arterial wall,” J. Biomed. Opt. 16(2), 026005 (2011). [CrossRef] [PubMed]

11

11. Z. Hajjarian and S. K. Nadkarni, “Evaluation and Correction for Optical Scattering Variations in Laser Speckle Rheology of Biological Fluids,” PLoS ONE 8(5), e65014 (2013). [CrossRef] [PubMed]

]. Our goal in this study is to investigate the influence of absorption and scattering on the accuracy of LSR measurements. More specifically, we demonstrate that speckle modulation by μa and μs' variations, in samples of identical mechanical properties, complicates the analysis of g2(t) curve for deducing the MSD, and induces inaccuracies in the estimated viscoelastic moduli [11

11. Z. Hajjarian and S. K. Nadkarni, “Evaluation and Correction for Optical Scattering Variations in Laser Speckle Rheology of Biological Fluids,” PLoS ONE 8(5), e65014 (2013). [CrossRef] [PubMed]

, 22

22. A. Mazhar, D. J. Cuccia, T. B. Rice, S. A. Carp, A. J. Durkin, D. A. Boas, B. Choi, and B. J. Tromberg, “Laser speckle imaging in the spatial frequency domain,” Biomed. Opt. Express 2(6), 1553–1563 (2011). [CrossRef] [PubMed]

].

The necessity of incorporating optical properties in the analysis of laser speckle contrast for blood flow quantification has been investigated by others [22

22. A. Mazhar, D. J. Cuccia, T. B. Rice, S. A. Carp, A. J. Durkin, D. A. Boas, B. Choi, and B. J. Tromberg, “Laser speckle imaging in the spatial frequency domain,” Biomed. Opt. Express 2(6), 1553–1563 (2011). [CrossRef] [PubMed]

, 26

26. T. B. Rice, S. D. Konecky, A. Mazhar, D. J. Cuccia, A. J. Durkin, B. Choi, and B. J. Tromberg, “Quantitative determination of dynamical properties using coherent spatial frequency domain imaging,” J. Opt. Soc. Am. A 28(10), 2108–2114 (2011). [CrossRef] [PubMed]

]. Theoretically, speckle contrast may be recovered from g2(t) through temporal integration. Nonetheless, the inverse is not true, and the g2(t) curve cannot be directly inferred from speckle contrast measurements. Thus, findings of these past studies are not directly applicable to the problem of assessing viscoelasticity from speckle fluctuations encountered in LSR. In [20

20. D. A. Boas and A. G. Yodh, “Spatially varying dynamical properties of turbid media probed with diffusing temporal light correlation,” J. Opt. Soc. Am. A 14(1), 192–215 (1997). [CrossRef]

], authors had a glimpse at speckle modulation induced by μs' variations. Nonetheless, the role of μa was not discussed. To address the confounding effect of both μa and μs' variations on speckle modulation, we compare the capability of DWS formalisms and Monte-Carlo based approaches, to deduce the MSD of scattering particles and eventually the viscoelastic modulus from g2(t) curves. A key result of this work is that for samples with non-negligible, moderate μa, DWS exhibits fortuitously accurate results and mirrors the computationally intensive PSCT-MCRT approach in its capability to measure MSD. The reasonable accuracy of the simpler and computationally convenient DWS solution for speckle analysis opens the possibility for real-time and rapid assessment of sample mechanical properties using LSR for chemical, industrial and biomedical applications.

The glycerol phantoms studied here have a large range of μa (0.14-9.95 mm−1) and μs' (1.2-129.2 mm−1) values similar to soft tissues and bio-fluids, as well as coatings, creams, emulsions, and paints in the visible/near-infrared window [1

1. D. A. Weitz and D. J. Pine, “Diffusing-Wave Spectroscopy,” in Dynamic Light Scattering: The Methods and Some Applications, W. Brown, ed. (Oxford University, 1993) (49).

5

5. A. Brun, H. Dihang, and L. Brunel, “Film formation of coatings studied by diffusing-wave spectroscopy,” Prog. Org. Coat. 61(2-4), 181–191 (2008). [CrossRef]

]. We have exploited Mie theory to calculate μa and μs' of these phantoms [23

23. L. V. Wang and H. Wu, Biomedical optics: principles and imaging (Wiley-Interscience, 2007).

]. In practice, when conducting LSR in viscoelastic materials, like tissue, optical properties may be evaluated experimentally. We have previously shown that by temporal averaging of speckle frames, the diffuse reflectance profile (DRP) of the scattered light may be calculated. Then μa and μs' may be extracted by fitting the DRP to a model derived from steady state diffusion theory [7

7. S. K. Nadkarni, A. Bilenca, B. E. Bouma, and G. J. Tearney, “Measurement of fibrous cap thickness in atherosclerotic plaques by spatiotemporal analysis of laser speckle images,” J. Biomed. Opt. 11(2), 021006 (2006). [CrossRef] [PubMed]

, 11

11. Z. Hajjarian and S. K. Nadkarni, “Evaluation and Correction for Optical Scattering Variations in Laser Speckle Rheology of Biological Fluids,” PLoS ONE 8(5), e65014 (2013). [CrossRef] [PubMed]

, 32

32. T. J. Farrell, M. S. Patterson, and B. Wilson, “A diffusion theory model of spatially resolved, steady-state diffuse reflectance for the noninvasive determination of tissue optical properties in vivo,” Med. Phys. 19(4), 879–888 (1992). [CrossRef] [PubMed]

].

In glycerol phantoms, studied here, the MSD depends on the viscosity of the solvent and the radius of Carbon and TiO2 particles, a. Besides, optical properties may be expressed using Mie theory as [23

23. L. V. Wang and H. Wu, Biomedical optics: principles and imaging (Wiley-Interscience, 2007).

]:
μa=ρCarbonσACarbon+ρTiO2σATiO2μs'=(ρCarbonσSCarbon+ρTiO2σSTiO2)(1g)
(5)
Here, ρ, σA and σS represent the number-density and absorption and scattering cross sections of the Carbon and TiO2 particles and g is the anisotropy factor. Both σA and σS are complex functions of source wavelength, refractive index mismatch, and the particle size, a. Therefore, by investigating the role of optical properties in speckle modulation, we also indirectly consider the contribution of particle size. Since variations of a, alter both µa and μs', it is challenging to distinguish the effect of particle size, alone, on speckle fluctuations. To determine the viscoelastic modulus, the influence of particle size is isolated by substituting a in the GSER (Eq. (4)) to accurately deduce G*(ω) from the MSD [14

14. T. G. Mason and D. A. Weitz, “Optical measurements of frequency-dependent linear viscoelastic moduli of complex fluids,” Phys. Rev. Lett. 74(7), 1250–1253 (1995). [CrossRef] [PubMed]

19

19. M. Jonas, H. Huang, R. D. Kamm, and P. T. So, “Fast fluorescence laser tracking microrheometry. I: instrument development,” Biophys. J. 94(4), 1459–1469 (2008). [CrossRef] [PubMed]

]. The GSER approximation is sufficiently accurate in homogenous viscous glycerol phantoms. Close agreement between LSR measurements of G*(ω) and the reference-standard rheometry, observed in Figs. 3, 5, 7, and 8, further confirms the validity of GSER. To enable LSR measurements in substances where scattering size in not known before hand, such as tissue, supplementary components may be integrated in the LSR setup to estimate the particle size distribution, for instance by analyzing the angle-resolved low coherence radiation or by processing the angular dependence of the diffuse intensity at multiple polarization states [33

33. M. Giacomelli, Y. Zhu, J. Lee, and A. Wax, “Size and shape determination of spheroidal scatterers using two-dimensional angle resolved scattering,” Opt. Express 18(14), 14616–14626 (2010). [CrossRef] [PubMed]

, 34

34. A. H. Hielscher, J. R. Mourant, and I. J. Bigio, “Influence of particle size and concentration on the diffuse backscattering of polarized light from tissue phantoms and biological cell suspensions,” Appl. Opt. 36(1), 125–135 (1997). [CrossRef] [PubMed]

].

In early DLS studies for particle sizing applications, digital correlators have been exploited to calculate the g2(t) curve of the light collected over a single speckle spot by a photomultiplier tube (PMT) or a photodiode (PD) [1

1. D. A. Weitz and D. J. Pine, “Diffusing-Wave Spectroscopy,” in Dynamic Light Scattering: The Methods and Some Applications, W. Brown, ed. (Oxford University, 1993) (49).

]. Utilizing the intensity of only one coherent area, necessitates temporal averaging of several g2(t) curves and acquisition times of several minutes to hours. The high speed CMOS camera, used for multi-speckle acquisition here, improves the statistical accuracy of the measured g2(t) and eliminates the need for long-time acquisition [6

6. S. K. Nadkarni, B. E. Bouma, T. Helg, R. Chan, E. Halpern, A. Chau, M. S. Minsky, J. T. Motz, S. L. Houser, and G. J. Tearney, “Characterization of atherosclerotic plaques by laser speckle imaging,” Circulation 112(6), 885–892 (2005). [CrossRef] [PubMed]

12

12. L. Cipelletti and D. A. Weitz, “Ultralow angle dynamic light scattering with a charge coupled device camera based multispeckle multitau correlator,” Rev. Sci. Instrum. 70(8), 3214–3221 (1999). [CrossRef]

].

In the current LSR setup, the 50 µm illumination beam is located at the center of the 2 mm FOV. Fluctuations of acquired speckle spots are likely influenced by distance from the illumination center. For instance in highly scattering samples, rays remitted further away from the illumination center travel longer optical paths and likely increase the rate of speckle fluctuations at peripheral regions of the FOV. In addition, cross-polarized collection of the scattered light, filters out both specular reflection and single-scattered light, enhancing the contribution of multiply scattered light on speckle fluctuations. In contrast, for strongly absorbing samples, where longer paths are significantly pruned, most of the back-scattered photons escape the sample at the vicinity of illumination center and location-dependence modulation of speckle is reduced. Equations (2) and (3), derived using DWS formalism and MCRT-based approach, incorporate the implications of path length distribution by integrating the autocorrelation function of individual light paths over the entire distribution. Equivalently, in experimental evaluation of g2(t) spatial averaging over the entire FOV reduces the influence of path length variability in the calculation of g2(t) (Eq. (1)).

Figures 3(b), 5(b), 7(b), and 8(b) demonstrate that PSCT-MCRT simulations, which take into account the illumination/detection configuration, optical properties, and polarization state provide the most accurate estimate of the MSD and the sample viscoelasticity for any arbitrary choice of optical properties [11

11. Z. Hajjarian and S. K. Nadkarni, “Evaluation and Correction for Optical Scattering Variations in Laser Speckle Rheology of Biological Fluids,” PLoS ONE 8(5), e65014 (2013). [CrossRef] [PubMed]

, 35

35. P. A. Lemieux, M. U. Vera, and D. J. Durian, “Diffusing-light spectroscopies beyond the diffusion limit:The role of ballistic transport and anisotropic scattering,” Phys. Rev. E Stat. Phys. Plasmas Fluids Relat. Interdiscip. Topics 57(4), 4498–4515 (1998). [CrossRef]

]. The PSCT-MCRT approach, although computationally intensive, accurately tracks photons in the turbid medium of known optical properties and computes the total momentum transfer Y = ∑q2/(2k02) [11

11. Z. Hajjarian and S. K. Nadkarni, “Evaluation and Correction for Optical Scattering Variations in Laser Speckle Rheology of Biological Fluids,” PLoS ONE 8(5), e65014 (2013). [CrossRef] [PubMed]

]. As a result, in all cases it provides similar or superior accuracy compared to DWS.

An alternative analytical solution, termed telegrapher equation, has been proposed that is slightly more complex than DWS but supposedly treats the strong absorption and non-diffusive propagation in weakly scattering samples with more accuracy [35

35. P. A. Lemieux, M. U. Vera, and D. J. Durian, “Diffusing-light spectroscopies beyond the diffusion limit:The role of ballistic transport and anisotropic scattering,” Phys. Rev. E Stat. Phys. Plasmas Fluids Relat. Interdiscip. Topics 57(4), 4498–4515 (1998). [CrossRef]

]. It also accounts for scattering anisotropy by making the localized area around the light source devoid of diffused photons to emulate the forwardly directed anisotropic scattering of photons. In this way, photon migrations at various distances from the source are treated differently. Despite all these modifications, our preliminary experiments illustrated that the telegrapher equation does not exhibit a significant improvement over DWS [35

35. P. A. Lemieux, M. U. Vera, and D. J. Durian, “Diffusing-light spectroscopies beyond the diffusion limit:The role of ballistic transport and anisotropic scattering,” Phys. Rev. E Stat. Phys. Plasmas Fluids Relat. Interdiscip. Topics 57(4), 4498–4515 (1998). [CrossRef]

]. The demonstrated efficacy of DWS formalism obviates the need for a more complex Monte-Carlo Ray Tracing approach, whenever noticeable absorption exists and the ratio μa/μs' < 0.1. The current development on correcting for the influence of optical properties helps to significantly improve the performance and accuracy of LSR to measure the mechanical properties of a variety of materials including biological tissue.

Acknowledgments

This study was funded by the NIH grant No. R21 HL 088306 (S.N), NIH grant No. U54 EB015408-01 (S.N), and the ARRA grant No. R21 HL 088306-02S1 (S.N).

References and links

1.

D. A. Weitz and D. J. Pine, “Diffusing-Wave Spectroscopy,” in Dynamic Light Scattering: The Methods and Some Applications, W. Brown, ed. (Oxford University, 1993) (49).

2.

M. M. Robins, A. D. Watson, and P. J. Wilde, “Emulsions-creaming and rheology,” Curr. Opin. Colloid Interface Sci. 7(5-6), 419–425 (2002). [CrossRef]

3.

M. Alexander and D. G. Dalgleish, “Application of transmission diffusing wave spectroscopy to the study of gelation of milk by acidification and rennet,” Colloids Surf. B Biointerfaces 38(1-2), 83–90 (2004). [CrossRef] [PubMed]

4.

A. J. Breugem, F. Bouchama, and G. J. M. Koper, “Diffusing wave spectroscopy: A novel rheological method for drying paint films,” Surf. Coat. Int. B 88(2), 135–138 (2005). [CrossRef]

5.

A. Brun, H. Dihang, and L. Brunel, “Film formation of coatings studied by diffusing-wave spectroscopy,” Prog. Org. Coat. 61(2-4), 181–191 (2008). [CrossRef]

6.

S. K. Nadkarni, B. E. Bouma, T. Helg, R. Chan, E. Halpern, A. Chau, M. S. Minsky, J. T. Motz, S. L. Houser, and G. J. Tearney, “Characterization of atherosclerotic plaques by laser speckle imaging,” Circulation 112(6), 885–892 (2005). [CrossRef] [PubMed]

7.

S. K. Nadkarni, A. Bilenca, B. E. Bouma, and G. J. Tearney, “Measurement of fibrous cap thickness in atherosclerotic plaques by spatiotemporal analysis of laser speckle images,” J. Biomed. Opt. 11(2), 021006 (2006). [CrossRef] [PubMed]

8.

S. K. Nadkarni, B. E. Bouma, D. Yelin, A. Gulati, and G. J. Tearney, “Laser speckle imaging of atherosclerotic plaques through optical fiber bundles,” J. Biomed. Opt. 13(5), 054016 (2008). [CrossRef] [PubMed]

9.

Z. Hajjarian, J. Xi, F. A. Jaffer, G. J. Tearney, and S. K. Nadkarni, “Intravascular laser speckle imaging catheter for the mechanical evaluation of the arterial wall,” J. Biomed. Opt. 16(2), 026005 (2011). [CrossRef] [PubMed]

10.

Z. Hajjarian and S. K. Nadkarni, “Evaluating the viscoelastic properties of tissue from laser speckle fluctuations,” Sci. Rep. 2, 316 (2012). [CrossRef] [PubMed]

11.

Z. Hajjarian and S. K. Nadkarni, “Evaluation and Correction for Optical Scattering Variations in Laser Speckle Rheology of Biological Fluids,” PLoS ONE 8(5), e65014 (2013). [CrossRef] [PubMed]

12.

L. Cipelletti and D. A. Weitz, “Ultralow angle dynamic light scattering with a charge coupled device camera based multispeckle multitau correlator,” Rev. Sci. Instrum. 70(8), 3214–3221 (1999). [CrossRef]

13.

D. J. Pine, D. A. Weitz, J. X. Zhu, and E. Herbolzheimer, “Diffusing-wave spectroscopy: dynamic light scattering in the multiple scattering limit,” J. Phys. France 51, 2101–2127 (1990).

14.

T. G. Mason and D. A. Weitz, “Optical measurements of frequency-dependent linear viscoelastic moduli of complex fluids,” Phys. Rev. Lett. 74(7), 1250–1253 (1995). [CrossRef] [PubMed]

15.

T. G. Mason, H. Gang, and D. A. Weitz, “Diffusing-wave-spectroscopy measurements of viscoelasticity of complex fluids,” J. Opt. Soc. Am. A 14(1), 139–149 (1997). [CrossRef]

16.

T. G. Mason, “Estimating the viscoelastic moduli of complex fluids using the generalized Stokes-Einstein equation,” Rheol. Acta 39(4), 371–378 (2000). [CrossRef]

17.

B. R. Dasgupta, S. Y. Tee, J. C. Crocker, B. J. Frisken, and D. A. Weitz, “Microrheology of polyethylene oxide using diffusing wave spectroscopy and single scattering,” Phys. Rev. E Stat. Nonlin. Soft Matter Phys. 65(5), 051505 (2002). [CrossRef] [PubMed]

18.

B. R. Dasgupta and D. A. Weitz, “Microrheology of cross-linked polyacrylamide networks,” Phys. Rev. E Stat. Nonlin. Soft Matter Phys. 71(2), 021504 (2005). [CrossRef] [PubMed]

19.

M. Jonas, H. Huang, R. D. Kamm, and P. T. So, “Fast fluorescence laser tracking microrheometry. I: instrument development,” Biophys. J. 94(4), 1459–1469 (2008). [CrossRef] [PubMed]

20.

D. A. Boas and A. G. Yodh, “Spatially varying dynamical properties of turbid media probed with diffusing temporal light correlation,” J. Opt. Soc. Am. A 14(1), 192–215 (1997). [CrossRef]

21.

D. Irwin, L. Dong, Y. Shang, R. Cheng, M. Kudrimoti, S. D. Stevens, and G. Yu, “Influences of tissue absorption and scattering on diffuse correlation spectroscopy blood flow measurements,” Biomed. Opt. Express 2(7), 1969–1985 (2011). [CrossRef] [PubMed]

22.

A. Mazhar, D. J. Cuccia, T. B. Rice, S. A. Carp, A. J. Durkin, D. A. Boas, B. Choi, and B. J. Tromberg, “Laser speckle imaging in the spatial frequency domain,” Biomed. Opt. Express 2(6), 1553–1563 (2011). [CrossRef] [PubMed]

23.

L. V. Wang and H. Wu, Biomedical optics: principles and imaging (Wiley-Interscience, 2007).

24.

F. Cardinaux, L. Cipelletti, F. Scheffold, and P. Schurtenberger, “Micreorheology of giant-micelle solutions,” Europhys. Lett. 57(5), 738–744 (2002). [CrossRef]

25.

S. Sakadzić and L. V. Wang, “Correlation transfer equation for multiply scattered light modulated by an ultrasonic pulse,” J. Opt. Soc. Am. A 24(9), 2797–2806 (2007). [CrossRef] [PubMed]

26.

T. B. Rice, S. D. Konecky, A. Mazhar, D. J. Cuccia, A. J. Durkin, B. Choi, and B. J. Tromberg, “Quantitative determination of dynamical properties using coherent spatial frequency domain imaging,” J. Opt. Soc. Am. A 28(10), 2108–2114 (2011). [CrossRef] [PubMed]

27.

S. T. Flock, S. L. Jacques, B. C. Wilson, W. M. Star, and M. J. van Gemert, “Optical properties of Intralipid: a phantom medium for light propagation studies,” Lasers Surg. Med. 12(5), 510–519 (1992). [CrossRef] [PubMed]

28.

W. R. Calhoun, H. Maeta, S. Roy, L. M. Bali, and S. Bali, “Sensitive real-time measurement of the refractive index and attenuation coefficient of milk and milk-cream mixtures,” J. Dairy Sci. 93(8), 3497–3504 (2010). [CrossRef] [PubMed]

29.

G. Latour, M. Elias, and J.-M. Frigerio, “Determination of the Absorption and Scattering Coefficients of Pigments: Application to the Identification of the Components of Pigment Mixtures,” Appl. Spectrosc. 63(6), 604–610 (2009). [CrossRef] [PubMed]

30.

D. J. Durian, “Accuracy of diffusing-wave spectroscopy theories,” Phys. Rev. E Stat. Phys. Plasmas Fluids Relat. Interdiscip. Topics 51(4), 3350–3358 (1995). [CrossRef] [PubMed]

31.

V. V. Tuchin, Handbook of optical biomedical diagnostics (SPIE Press, 2002).

32.

T. J. Farrell, M. S. Patterson, and B. Wilson, “A diffusion theory model of spatially resolved, steady-state diffuse reflectance for the noninvasive determination of tissue optical properties in vivo,” Med. Phys. 19(4), 879–888 (1992). [CrossRef] [PubMed]

33.

M. Giacomelli, Y. Zhu, J. Lee, and A. Wax, “Size and shape determination of spheroidal scatterers using two-dimensional angle resolved scattering,” Opt. Express 18(14), 14616–14626 (2010). [CrossRef] [PubMed]

34.

A. H. Hielscher, J. R. Mourant, and I. J. Bigio, “Influence of particle size and concentration on the diffuse backscattering of polarized light from tissue phantoms and biological cell suspensions,” Appl. Opt. 36(1), 125–135 (1997). [CrossRef] [PubMed]

35.

P. A. Lemieux, M. U. Vera, and D. J. Durian, “Diffusing-light spectroscopies beyond the diffusion limit:The role of ballistic transport and anisotropic scattering,” Phys. Rev. E Stat. Phys. Plasmas Fluids Relat. Interdiscip. Topics 57(4), 4498–4515 (1998). [CrossRef]

36.

S. L. Jacques and B. W. Pogue, “Tutorial on diffuse light transport,” J. Biomed. Opt. 13(4), 041302 (2008). [CrossRef] [PubMed]

37.

D. A. Boas, C. Pitris, and N. Ramanujam, Handbook of biomedical optics (CRC Press, 2011).

OCIS Codes
(110.6150) Imaging systems : Speckle imaging
(170.3660) Medical optics and biotechnology : Light propagation in tissues
(170.3880) Medical optics and biotechnology : Medical and biological imaging
(290.1990) Scattering : Diffusion
(290.4210) Scattering : Multiple scattering
(300.1030) Spectroscopy : Absorption

ToC Category:
Medical Optics and Biotechnology

History
Original Manuscript: December 26, 2013
Revised Manuscript: February 9, 2014
Manuscript Accepted: February 26, 2014
Published: March 11, 2014

Virtual Issues
Vol. 9, Iss. 5 Virtual Journal for Biomedical Optics

Citation
Zeinab Hajjarian and Seemantini K. Nadkarni, "Correction of optical absorption and scattering variations in laser speckle rheology measurements," Opt. Express 22, 6349-6361 (2014)
http://www.opticsinfobase.org/vjbo/abstract.cfm?URI=oe-22-6-6349


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References

  1. D. A. Weitz and D. J. Pine, “Diffusing-Wave Spectroscopy,” in Dynamic Light Scattering: The Methods and Some Applications, W. Brown, ed. (Oxford University, 1993) (49).
  2. M. M. Robins, A. D. Watson, P. J. Wilde, “Emulsions-creaming and rheology,” Curr. Opin. Colloid Interface Sci. 7(5-6), 419–425 (2002). [CrossRef]
  3. M. Alexander, D. G. Dalgleish, “Application of transmission diffusing wave spectroscopy to the study of gelation of milk by acidification and rennet,” Colloids Surf. B Biointerfaces 38(1-2), 83–90 (2004). [CrossRef] [PubMed]
  4. A. J. Breugem, F. Bouchama, G. J. M. Koper, “Diffusing wave spectroscopy: A novel rheological method for drying paint films,” Surf. Coat. Int. B 88(2), 135–138 (2005). [CrossRef]
  5. A. Brun, H. Dihang, L. Brunel, “Film formation of coatings studied by diffusing-wave spectroscopy,” Prog. Org. Coat. 61(2-4), 181–191 (2008). [CrossRef]
  6. S. K. Nadkarni, B. E. Bouma, T. Helg, R. Chan, E. Halpern, A. Chau, M. S. Minsky, J. T. Motz, S. L. Houser, G. J. Tearney, “Characterization of atherosclerotic plaques by laser speckle imaging,” Circulation 112(6), 885–892 (2005). [CrossRef] [PubMed]
  7. S. K. Nadkarni, A. Bilenca, B. E. Bouma, G. J. Tearney, “Measurement of fibrous cap thickness in atherosclerotic plaques by spatiotemporal analysis of laser speckle images,” J. Biomed. Opt. 11(2), 021006 (2006). [CrossRef] [PubMed]
  8. S. K. Nadkarni, B. E. Bouma, D. Yelin, A. Gulati, G. J. Tearney, “Laser speckle imaging of atherosclerotic plaques through optical fiber bundles,” J. Biomed. Opt. 13(5), 054016 (2008). [CrossRef] [PubMed]
  9. Z. Hajjarian, J. Xi, F. A. Jaffer, G. J. Tearney, S. K. Nadkarni, “Intravascular laser speckle imaging catheter for the mechanical evaluation of the arterial wall,” J. Biomed. Opt. 16(2), 026005 (2011). [CrossRef] [PubMed]
  10. Z. Hajjarian, S. K. Nadkarni, “Evaluating the viscoelastic properties of tissue from laser speckle fluctuations,” Sci. Rep. 2, 316 (2012). [CrossRef] [PubMed]
  11. Z. Hajjarian, S. K. Nadkarni, “Evaluation and Correction for Optical Scattering Variations in Laser Speckle Rheology of Biological Fluids,” PLoS ONE 8(5), e65014 (2013). [CrossRef] [PubMed]
  12. L. Cipelletti, D. A. Weitz, “Ultralow angle dynamic light scattering with a charge coupled device camera based multispeckle multitau correlator,” Rev. Sci. Instrum. 70(8), 3214–3221 (1999). [CrossRef]
  13. D. J. Pine, D. A. Weitz, J. X. Zhu, E. Herbolzheimer, “Diffusing-wave spectroscopy: dynamic light scattering in the multiple scattering limit,” J. Phys. France 51, 2101–2127 (1990).
  14. T. G. Mason, D. A. Weitz, “Optical measurements of frequency-dependent linear viscoelastic moduli of complex fluids,” Phys. Rev. Lett. 74(7), 1250–1253 (1995). [CrossRef] [PubMed]
  15. T. G. Mason, H. Gang, D. A. Weitz, “Diffusing-wave-spectroscopy measurements of viscoelasticity of complex fluids,” J. Opt. Soc. Am. A 14(1), 139–149 (1997). [CrossRef]
  16. T. G. Mason, “Estimating the viscoelastic moduli of complex fluids using the generalized Stokes-Einstein equation,” Rheol. Acta 39(4), 371–378 (2000). [CrossRef]
  17. B. R. Dasgupta, S. Y. Tee, J. C. Crocker, B. J. Frisken, D. A. Weitz, “Microrheology of polyethylene oxide using diffusing wave spectroscopy and single scattering,” Phys. Rev. E Stat. Nonlin. Soft Matter Phys. 65(5), 051505 (2002). [CrossRef] [PubMed]
  18. B. R. Dasgupta, D. A. Weitz, “Microrheology of cross-linked polyacrylamide networks,” Phys. Rev. E Stat. Nonlin. Soft Matter Phys. 71(2), 021504 (2005). [CrossRef] [PubMed]
  19. M. Jonas, H. Huang, R. D. Kamm, P. T. So, “Fast fluorescence laser tracking microrheometry. I: instrument development,” Biophys. J. 94(4), 1459–1469 (2008). [CrossRef] [PubMed]
  20. D. A. Boas, A. G. Yodh, “Spatially varying dynamical properties of turbid media probed with diffusing temporal light correlation,” J. Opt. Soc. Am. A 14(1), 192–215 (1997). [CrossRef]
  21. D. Irwin, L. Dong, Y. Shang, R. Cheng, M. Kudrimoti, S. D. Stevens, G. Yu, “Influences of tissue absorption and scattering on diffuse correlation spectroscopy blood flow measurements,” Biomed. Opt. Express 2(7), 1969–1985 (2011). [CrossRef] [PubMed]
  22. A. Mazhar, D. J. Cuccia, T. B. Rice, S. A. Carp, A. J. Durkin, D. A. Boas, B. Choi, B. J. Tromberg, “Laser speckle imaging in the spatial frequency domain,” Biomed. Opt. Express 2(6), 1553–1563 (2011). [CrossRef] [PubMed]
  23. L. V. Wang and H. Wu, Biomedical optics: principles and imaging (Wiley-Interscience, 2007).
  24. F. Cardinaux, L. Cipelletti, F. Scheffold, P. Schurtenberger, “Micreorheology of giant-micelle solutions,” Europhys. Lett. 57(5), 738–744 (2002). [CrossRef]
  25. S. Sakadzić, L. V. Wang, “Correlation transfer equation for multiply scattered light modulated by an ultrasonic pulse,” J. Opt. Soc. Am. A 24(9), 2797–2806 (2007). [CrossRef] [PubMed]
  26. T. B. Rice, S. D. Konecky, A. Mazhar, D. J. Cuccia, A. J. Durkin, B. Choi, B. J. Tromberg, “Quantitative determination of dynamical properties using coherent spatial frequency domain imaging,” J. Opt. Soc. Am. A 28(10), 2108–2114 (2011). [CrossRef] [PubMed]
  27. S. T. Flock, S. L. Jacques, B. C. Wilson, W. M. Star, M. J. van Gemert, “Optical properties of Intralipid: a phantom medium for light propagation studies,” Lasers Surg. Med. 12(5), 510–519 (1992). [CrossRef] [PubMed]
  28. W. R. Calhoun, H. Maeta, S. Roy, L. M. Bali, S. Bali, “Sensitive real-time measurement of the refractive index and attenuation coefficient of milk and milk-cream mixtures,” J. Dairy Sci. 93(8), 3497–3504 (2010). [CrossRef] [PubMed]
  29. G. Latour, M. Elias, J.-M. Frigerio, “Determination of the Absorption and Scattering Coefficients of Pigments: Application to the Identification of the Components of Pigment Mixtures,” Appl. Spectrosc. 63(6), 604–610 (2009). [CrossRef] [PubMed]
  30. D. J. Durian, “Accuracy of diffusing-wave spectroscopy theories,” Phys. Rev. E Stat. Phys. Plasmas Fluids Relat. Interdiscip. Topics 51(4), 3350–3358 (1995). [CrossRef] [PubMed]
  31. V. V. Tuchin, Handbook of optical biomedical diagnostics (SPIE Press, 2002).
  32. T. J. Farrell, M. S. Patterson, B. Wilson, “A diffusion theory model of spatially resolved, steady-state diffuse reflectance for the noninvasive determination of tissue optical properties in vivo,” Med. Phys. 19(4), 879–888 (1992). [CrossRef] [PubMed]
  33. M. Giacomelli, Y. Zhu, J. Lee, A. Wax, “Size and shape determination of spheroidal scatterers using two-dimensional angle resolved scattering,” Opt. Express 18(14), 14616–14626 (2010). [CrossRef] [PubMed]
  34. A. H. Hielscher, J. R. Mourant, I. J. Bigio, “Influence of particle size and concentration on the diffuse backscattering of polarized light from tissue phantoms and biological cell suspensions,” Appl. Opt. 36(1), 125–135 (1997). [CrossRef] [PubMed]
  35. P. A. Lemieux, M. U. Vera, D. J. Durian, “Diffusing-light spectroscopies beyond the diffusion limit:The role of ballistic transport and anisotropic scattering,” Phys. Rev. E Stat. Phys. Plasmas Fluids Relat. Interdiscip. Topics 57(4), 4498–4515 (1998). [CrossRef]
  36. S. L. Jacques, B. W. Pogue, “Tutorial on diffuse light transport,” J. Biomed. Opt. 13(4), 041302 (2008). [CrossRef] [PubMed]
  37. D. A. Boas, C. Pitris, and N. Ramanujam, Handbook of biomedical optics (CRC Press, 2011).

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