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Opt Lett. Author manuscript; available in PMC 2012 December 15.

Published in final edited form as:

Opt Lett. 2011 December 15; 36(24): 4737–4739.

PMCID: PMC3355761

NIHMSID: NIHMS376347

Andrew J. Radosevich,^{1,}^{*} Nikhil N. Mutyal,^{1} Vladimir Turzhitsky,^{1} Jeremy D. Rogers,^{1} Ji Yi,^{1} Allen Taflove,^{2} and Vadim Backman^{1}

See other articles in PMC that cite the published article.

In this Letter, we describe an easy to implement technique to measure the spatial backscattering impulse-response at length-scales shorter than a transport mean free path with resolution of better than 10 μm using the enhanced backscattering (EBS) phenomenon. This technique enables spectroscopic measurements throughout the visible range and sensitivity to all polarization channels. Through a combination of Monte Carlo simulations and experimental measurements of latex microspheres, we explore the various sensitivities of our technique to both intrinsic sample properties and extrinsic instrumental properties. We conclude by demonstrating the extraordinary sensitivity of our technique to the shape of the scattering phase function, including higher order shape parameters than the anisotropy factor (or first moment).

The spatial backscattering impulse-response at length-scales shorter than a transport mean free path is highly sensitive to the shape of the scattering phase function due to the fact that rays exiting within this regime have undergone relatively few scattering events. Typically this measurement is accomplished using a lens to focus the illumination beam to a near impulse on the sample surface. A CCD camera then detects the spatial distribution of backscattered light at the sample surface. With this design, the full azimuthal backscattering distribution can easily be measured for each polarization channel [1]. Still, a true impulse can never be achieved and information at short length-scales is lost to an optical mask (~mm diameter) needed to reject specular reflections. Thus in media such as biological tissue with long on the order of 1 mm, information about the shape of the phase function is extremely difficult to measure experimentally. As an alternative to overcome these difficulties, here we report a simple bench-top instrument using polarized enhanced backscattering (EBS) to first measure the backscattering distribution in the angular domain and subsequently convert to the spatial domain through inverse Fourier transformation.

EBS is an angular intensity peak centered in the exact backscattering direction that is formed by the summed diffraction pattern from all sets of time-reversed path-pairs within a scattering medium (a direct consequence of the reciprocity theorem) [2]. Conceptually, it is useful to think of each time-reversed path-pair as a single Young’s double pinhole experiment. For a single time-reversed path-pair with rays exiting at a particular spatial separation, the diffraction pattern is the Fourier transform of two delta functions (cosine pattern). For a semi-infinite medium under plane wave illumination the distribution of spatial separations for all time-reversed path-pairs is given by the spatial backscattering impulse-response for *multiply scattered light* in the *exact backward direction p(x,y)*. As a result, in an idealized case the EBS peak *I _{EBS}*(

(1)

where denotes the Fourier transform operation, *pc* specifies the degree of phase correlation between the forward and reverse path, *s* represents the effective distribution of rays which remain within the illumination spot, *c* is the spatial coherence function, and *mtf* is the modulation transfer function of the optical instrument. Within the operation, *p* and *pc* represent instrinsic sample properties while *s, c*, and *mtf* represent extrinsic instrument properties. Each of these functions will described in further detail in the following paragraphs.

The experimentally measurable *p _{eff}* is found by computing the inverse Fourier transform of the EBS peak:

(2)

For sample characterization, the functions *p* and *pc* are of prime interest. In principle these intrinsic parameters can be found by dividing *p _{eff}* by functions

Our experimental instrument is shown in Fig. 1. An illumination source (xenon lamp with finite spatial coherence length *L _{sc}* or broadband laser with

EBS instrument. Collimating lens L_{1} (*f* = 200 mm), linear polarizer P, mirror M, beam splitter B, quarter wave plate QWP, linear analyzer A, Fourier lens L_{2} (*f* = 100 mm), liquid crystal tunable filter LCTF.

Information regarding the processing of experimental and Monte Carlo simulated EBS data can be found in detail in other publications [3,4]. It should be noted that all experimental data is scaled by a constant multiplicative factor of 0.65 to obtain a full match with Monte Carlo simulation [4]. This type of one parameter fit is common in EBS literature [5]. In this Letter, all experiments and Monte Carlo simulations are for aqueous latex microsphere suspensions (10% solids by weight) which are diluted in DI water to achieve different values of
After retrieving the experimental EBS peak, the spatial distribution of backscattered light is computed using Eq. 2. According to the properties of the discrete Fourier transform, the spatial resolution Δ*s* is related to the angular resolution Δ*θ* by:

(3)

where λ is the illumination wavelength and *n* is the number of pixels in the *x* or *y* direction. Our instrument collects angles up to 7.5776° with 0.0074° resolution. Within the visible range of illumination this corresponds to a spatial extent of >1500 μm with <10 μm resolution.

Strictly speaking the reciprocity theorem is only fully valid for polarization preserving channels (i.e. linear co-polarized *xx* or helicity preserving *++*) [2]. For these channels, each ray has a time-reversed partner which exits with the same accumulated phase and *pc* = 1 for all x,y positions. However, in the orthogonal polarization channels (i.e. linear cross-polarized *xy* or opposite helicity *+-*) not all scattering rotations are reversible. As a result, the forward and reverse paths may exit with different phases and *pc* does not necessarily equal 1. Following the calculations of Ref. [6], *pc* in the orthogonal channels can be approximated from the degree of linear (
) and circular (
) polarization:

(4)

Figure 2a shows function *pc* for the four measured polarization channels. For very short length-scales, rays undergo relatively few scattering events and *pc* is nearly 1. As the exit radius increases, the average number of scattering events also increases. As a result, a greater proportion of rays travel through irreversible paths and *pc* → 0 as *r* → ∞ [2]. Figure 2b shows the excellent agreement between experiment and simulation for *p _{eff}* measured from each of the 4 polarization channels.

Polarization sensitivities. (a) Function *pc* for the 4 measured polarization channels as a function of exit radius. (b) Experimental (symbols) and simulation (lines) *p*_{eff}. Sample : 0.65μm diameter sphere with
= 205 μm at 633 nm. Spot **...**

Since realistic experiments have finite illumination beam extent, an effective distribution of rays which remain within the illumination spot (and therefore possess a time-reversed partner) must be found. This can be obtained by computing the normalized autocorrelation function *ACF* of the illumination pattern *A* incident on the scattering sample [4]:

(5)

In our case, a circular beam is used and A is a top hat function (i.e. A = 1 within the illumination spot and 0 otherwise). For each spot size, *s* begins at 1 and decreases to 0 when the path-pair separation is larger than the beam diameter. Figure 3a shows function *s* for 2 illumination spot sizes. Figure 3b shows excellent agreement between the experiment and simulation *p _{eff}* for 2000 and 7000 μm spot sizes.

Illumination beam spot size sensitivities. (a) *s* as a function of exit radius for 2 beam spot sizes. (b) Comparison between experiment (symbols) and simulation (lines) for the different beam spot sizes using *++* polarization. Sample : 0.65 μm diameter **...**

Another consideration for the measurement of *p _{eff}* is function

(6)

Figure 4a shows function *c* for illumination with 4 different *L _{sc}* possible with our instrument. Figure 4b shows the agreement between the experiment and simulation

Sensitivities to the spatial coherence of the illumination. (a) Function *c* for different *L*_{sc}. (b) Comparison between experiment (symbols) and simulation (lines) for different *L*_{sc} using *++* polarization. Sample : 0.65 μm diameter sphere with
= **...**

For any imaging system the *mtf* describes the ability to capture information from different spatial frequencies. As such, the measurement of *p _{eff}* will also be modulated by the

As a final demonstration of the sensitivity of our technique to fine details in the scattering phase function, we measure two suspensions of microspheres with the same
(1000 μm) and anisotropy factor *g* (0.87) but different size parameter *ka* (where *k* is the wavenumber in water and *a* is the microsphere radius). Figure 5a displays the two samples’ phase functions. Although they are generally similar in shape, the sample with higher *ka* has many higher frequency oscillations in accordance with Mie theory. In Fig. 5b we demonstrate that these higher frequency oscillations have a profound effect on the shape of *p _{eff}* at short length-scales. These slight differences are readily distinguishable using the technique presented in this Letter.

Sensitivity of EBS to the phase function. (a) Phase function for two microsphere samples with the same *g* but different *ka*. (b) Corresponding *p*_{eff} for *++* polarization shows a large difference in shape at short length-scales. *ka* ~ 4 : 0.65 μm diameter **...**

In summary we have presented EBS as a useful method to measure the backscattering impulse-response at small length-scales where information about the phase function is preserved. We first discussed the various sample dependent and experimental variables which affect the measurement and then provided a demonstration of its extraordinary sensitivity to the shape of the phase function.

This study was supported by National Institute of Health grant numbers RO1CA128641 and R01EB003682. A.J. Radosevich is supported by a National Science Foundation Graduate Research Fellowship under Grant No. DGE-0824162.

1. Hielscher A, Eick A, Mourant J, Shen D, Freyer J, Bigio I. Diffuse backscattering Mueller matrices of highly scattering media. Optic Express. 1997;1:441–453. [PubMed]

2. Lenke R, Maret G. Multiple scattering of light:coherent backscattering and transmission. In: Brown W, Mortensen K, editors. Scattering in Polymeric and Colloidal Systems. 2000.

3. Turzhitsky V, Rogers JD, Mutyal NN, Roy HK, Backman V. Characterization of light transport in scattering media at subdiffusion length scales with low-coherence enhanced backscattering. IEEE Journal of Selected Topics in Quantum Electronics. 2010;16:619–626. [PMC free article] [PubMed]

4. Radosevich AJ, Rogers JD, Turzhitsky V, Mutyal NN, Yi J, Roy HK, Backman V. Polarized enhanced backscattering spectroscopy for characterization of biological tissues at subdiffusion length-scales. IEEE J Sel Top Quantum Electron (2012) 2011 Oct 20; doc. ID JSTQE-INV-BIO2-04246-2011, in press. [PMC free article] [PubMed]

5. Ospeck M, Fraden S. Influence of reflecting boundaries and finite interfacial thickness on the coherent backscattering cone. Phys Rev E. 1994;49:4578. [PubMed]

6. Lenke R, Maret G. Magnetic field effects on coherent backscattering of light. European Physical Journal B. 2000;17:171–185.

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