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Optics Express

Optics Express

  • Editor: Andrew M. Weiner
  • Vol. 22, Iss. 9 — May. 5, 2014
  • pp: 10682–10692
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Modelization and optimized speckle detection scheme in photorefractive self-referenced acousto-optic imaging

Fabrice Devaux, Jean-Pierre Huignard, and François Ramaz  »View Author Affiliations


Optics Express, Vol. 22, Issue 9, pp. 10682-10692 (2014)
http://dx.doi.org/10.1364/OE.22.010682


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Abstract

A photorefractive BSO single crystal can be used for axially resolved acousto-optic imaging of thick scattering media in absence of a reference beam. This configuration renders the experimental setup easier to realize for imaging through thick scattering media with an improved optical etendue. We present here a model and simulations that explains these results. It is based on the spatial heterogeneity of the speckle pattern incident on the crystal. Optimization of the detector position and of the speckle grain size is confirmed by the model.

© 2014 Optical Society of America

1. Introduction

Optical imaging through thick biological tissues of several centimeters requires indirect methods in order to retrieve a millimeter resolution over the entire volume. The major drawback comes from scattering that generates multiple optical paths, so that the origin of the photons that propagate through the medium is lost. Many attempts have been made over the past few decades based on flux techniques such as diffuse optical tomography [1

1. S. R. Arridge, “Optical tomography in medical imaging,” Inverse Probl. 15, R41–R93 (1999). [CrossRef]

, 2

2. A. Bratchenia, R. Molenaar, T. G. van Leeuwen, and R. P. H. Kooyman, “Acousto-optic-assisted diffuse optical tomography,” Opt. Lett. 36, 1539–1541 (2011). [CrossRef] [PubMed]

], but the extraction of the signal is not straightforward, since it requires solving an inverse scattering problem. A more recent concept couples light with an ultrasonic beam within the medium [3

3. L. Wang, S. L. Jacques, and X. Zhao, “Continuous-wave ultrasonic modulation of scattered laser light to image objects in turbid media,” Opt. Lett. 20, 629–631 (1995). [CrossRef] [PubMed]

]. Dealing with the acousto-optic (AO) effect, the ultrasound (US) locally modulates the optical path, and thus the phase of light crossing the US field. This phase modulation mainly creates two weak optical sidebands (< 1%), shifted from the career frequency ωL of the US frequency +/ − ωUS. The magnitude of these so-called tagged photons depends on the optical properties of the medium, such as absorption and scattering. A 3D image of the optical properties of the medium is thus performed with a scan of the US beam. Mainly two approaches are implemented to detect the optical sidebands. The first one consists in a highly spectrally resolved flux measurement with a confocal Fabry-Perot interferometer [4

4. G. Rousseau, A. Blouin, and J.-P. Monchalin, “Ultrasound modulated optical imaging using a high-power pulsed laser and a double-pass confocal Fabry-Perot interferometer,” Opt. Lett. 34, 3445–3447 (2009). [CrossRef] [PubMed]

], or in spectral holeburning filtering at liquid helium temperature [5

5. X. Xu, S.-R. Kothapalli, H. Liu, and L. V. Wang, “Spectral hole burning for ultrasound-modulated optical tomography of thick tissue,” J. Biomed. Opt. 15, 066018 (2010). [CrossRef]

]. A second approach uses a coherent detection of the tagged photons, initially performed by digital off-axis holography with camera detection (CCD, CMOS) [6

6. M. Gross, P. Goy, and M. Al-Koussa, “Shot-noise detection of ultrasound-tagged photons in ultrasound-modulated optical imaging,” Opt. Lett. 28, 2482–2484 (2003). [CrossRef] [PubMed]

, 7

7. E. Benoit à la Guillaume, S. Farahi, E. Bossy, M. Gross, and F. Ramaz, “Acousto-optical coherence tomography with a digital holographic detection scheme,” Opt. Lett. 37, 3216–3218 (2012). [CrossRef] [PubMed]

]. This coherent detection requires accurate sampling of the speckle and the use of a fast camera, since the speckle decorrelates in living tissues on a millisecond time scale or less [8

8. A. Lev and B. Sfez, “In vivo demonstration of the ultrasound-modulated light technique,” J. Opt. Soc. Am. A 20, 2347–2354 (2003). [CrossRef]

]. For these reasons, wavefront adaptive setups have been implemented with photorefractive (PR) crystals and large-area single detectors, operating much faster than a camera [9

9. S. Farahi, E. Benoit à la Guillaume, A. A. Grabar, J.-P. Huignard, and F. Ramaz, “Time resolved three-dimensional acousto-optic imaging of thick scattering media,” Opt. Lett. 37, 2754–2756 (2012). [CrossRef] [PubMed]

]. In dynamic PR holography, a refractive index grating is recorded within the volume of the crystal, resulting from the interference between the tagged photons and a plane wave off-axis reference beam. Consequently, the reference diffracts a spatial replica of the tagged photons’ wavefront, which is time averaged according to the relative response time τPR of the crystal (1–20ms), depending on light irradiance (a few 100mW/cm2) [10

10. M. Lesaffre, F. Jean, F. Ramaz, A. C. Boccara, P. Delaye, and G. Roosen, “In situ monitoring of the photorefractive response time in a self-adaptive holography setup developed for acousto-optic imaging,” Opt. Express 15, 1030–1042 (2007). [CrossRef] [PubMed]

]. The use of a reference beam to record the hologram generally brings an important coherent background noise (beam fanning), which limits the signal-to-noise ratio (SNR) of detection, since the AO signal is less than two orders of magnitude compared to the DC-flux components when dynamic axial resolution along the ultrasonic beam is considered. In this paper, we will show that AO imaging with PR detection can also be performed without applying a reference beam onto the crystal. This type of interaction was demonstrated by Kamshilin et al. [11

11. A. A. Kamshilin, T. Jaaskelainen, and Y. N. Kulchin, “Adaptive correlation filter for stabilization of interference fiber optic sensors,” Appl. Phys. Lett. 73, 705–707 (1998). [CrossRef]

] for application of PR correlation filtering to the detection of vibrating rough surfaces or vibrating multimode fibers. The proof of principle for AO imaging is illustrated by Benoità la Guillaume et al. [12

12. E. Benoit à la Guillaume, U. Bortolozzo, J. P. Huignard, S. Residori, and F. Ramaz, “Dynamic ultrasound modulated optical tomography by self-referenced photorefractive holography,” Opt. Lett. 38, 287–289 (2013). [CrossRef] [PubMed]

] with a dynamic 2D image of ink inclusions embedded within 40mm of a multiply scattering phantom. The PR crystal used is the sillenite type Bi12SiO20 (BSO), known for its high photosensitivity in conventional holographic experiments in the blue-green spectral region. We outline that this configuration is much simpler to implement after having optimized the light-collection efficiency and the speckle size incident on the crystal. The experimental setup detailed in Ref. [12

12. E. Benoit à la Guillaume, U. Bortolozzo, J. P. Huignard, S. Residori, and F. Ramaz, “Dynamic ultrasound modulated optical tomography by self-referenced photorefractive holography,” Opt. Lett. 38, 287–289 (2013). [CrossRef] [PubMed]

] is shown in Fig. 1. We apply an excitation burst (carrier at 2.23 MHz) on the US transducer to get a good axial resolution of 1.35 mm while the lateral resolution, given by the tranverse profile of the US, is 2 mm. The used gel phantom has a reduced scattering coefficient μ′s of about 10 cm−1 with two included china ink cylinders to simulate local absorbers. The detection of the AO signal is performed with a large area photodiode of 3.6×3.6mm2 placed behind the optical system (L3L4) that improves the collection of the speckle light. As analyzed in [12

12. E. Benoit à la Guillaume, U. Bortolozzo, J. P. Huignard, S. Residori, and F. Ramaz, “Dynamic ultrasound modulated optical tomography by self-referenced photorefractive holography,” Opt. Lett. 38, 287–289 (2013). [CrossRef] [PubMed]

], the self referenced interaction can be interpreted as follows: in absence of US the incident speckled wavefront creates in the PR BSO a photoinduced space charge field which modulates the refractive index through the diffusion of carriers at no applied electric field. This complex phase volume hologram results from the interference of the incident speckle field with self-diffracted beam fanning noise fields. The speckle pattern photo-induces micrometer size random refractive index dots within the BSO volume. The operating conditions of the self-referenced PR holography for acousto-optic imaging are explained as follows: when the US transducer is off, the incident speckle field is perfectly phase matched with the recorded phase volume hologram. It thus results an optimum coherent diffraction on the detector. When the US transducer is now operating over short pulse duration the incident speckle structure is changed and it diffracts a wavefront which does not perfectly match with the complex phase hologram recorded in the volume of the BSO. In such conditions the diffracted intensity on the detector is reduced or enhanced as shown in [12

12. E. Benoit à la Guillaume, U. Bortolozzo, J. P. Huignard, S. Residori, and F. Ramaz, “Dynamic ultrasound modulated optical tomography by self-referenced photorefractive holography,” Opt. Lett. 38, 287–289 (2013). [CrossRef] [PubMed]

] and permits an acousto-optic imaging of a phantom embedded in the scattering medium. It was also shown experimentally in [12

12. E. Benoit à la Guillaume, U. Bortolozzo, J. P. Huignard, S. Residori, and F. Ramaz, “Dynamic ultrasound modulated optical tomography by self-referenced photorefractive holography,” Opt. Lett. 38, 287–289 (2013). [CrossRef] [PubMed]

] that in the case of self referenced holographic configuration an optimum signal detection is obtained when the two following conditions are fulfilled: first, the speckle grain size recorded in the PR crystal must be of the order of the Debye screening length. Second, the position of the detector in the transverse plane must be optimized due to the spatial frequency response of the photorefractive effect when speckle is involved. The objective of the paper is to develop hereafter an analytic model and numerical simulations which confirm these optimum conditions for signal detection in the conditions of self referenced speckle beam holography with a PR crystal operation at zero electric field.

Fig. 1 Experimental setup.

2. Theoretical model and numerical simulations

According to the experiment described in [12

12. E. Benoit à la Guillaume, U. Bortolozzo, J. P. Huignard, S. Residori, and F. Ramaz, “Dynamic ultrasound modulated optical tomography by self-referenced photorefractive holography,” Opt. Lett. 38, 287–289 (2013). [CrossRef] [PubMed]

], we first define the incident speckle field (i.e. the reference speckle field) and its intensity inside the BSO crystal respectively as: Sr(r) and Ir(r)= |Sr(r)|2, where r is the position vector inside the PR medium. This random distribution of coherent light intensity Ir photoinduces an internal space charge electric field in the whole volume of the PR crystal noted Esc(r). When the classical approximations are made in the PR model where electrons are considered as the single specy of charge carriers [13

13. P. Yeh, Introduction to Photorefractive Nonlinear Optics (John Wiley, 1993).

], the Ohm’s law governing the current density and the rate equations of the PR charge carriers lead to the following differential equation [14

14. O. Daniel, J.-M. C. Jonathan, and G. Roosen, “Photorefractrive effect in the Fourier plane,” Opt. Mater. 4, 294–298 (1995). [CrossRef]

, 15

15. O. Daniel, A. Stelmach, J.-M. C. Jonathan, and G. Roosen, “Whole-beam method analysis of photorefractive effect in correlators,” Opt. Commun. 113, 559–567 (1995). [CrossRef]

] :
Esc(r)1k02(Esc(r))=kBTeln[Ir(r)+Id],
(1)
where ∇ is the nabla operator, kB is the Boltzmann constant, T is the temperature, e is the elementary charge, k0 is the Debye screening wave number (typically for BSO k0 ≃ 4.65μm−1 [16

16. J. A. Gómez, H. Lorduy Gómez, and Á. Salazar, “Novel procedure for the simultaneous determination of the Debye length and electro-optic coefficient for an optically active photorefractive Bi12SiO20 crystal,” Opt. Commun. 284, 460–466 (2011). [CrossRef]

]) and Id is a uniform background illumination responsible of dark current photoconductivity. Using the Fourier transform properties, Eq. (1) becomes:
𝒯{Esc(r)}=kBTeik1+|k|2k02𝒯{ln[Ir(r+Id)]},
(2)
where ℱ𝒯 denotes the 3D Fourier transform and k is the wavevector. Assuming that the variation of the PR variables along the propagation axis can be neglected and a two-dimensional illumination where Ir(x, y) ≪ Id, Eq. (2) may be rewritten as:
{E˜scx(kt)=iαkx1+|kt|2k02I˜r(kt)E˜scy(kt)=iαky1+|kt|2k02I˜r(kt)
(3)
where scx(kt), scy(kt) and Ĩr(kt) are respectively the 2D Fourier transforms, calculated in the (x, y) plane, of the transverse components of the space charge field and of the speckle intensity. kt = kx + ky is the transverse component of the wavevector and α=kBTIde is a constant. These equations show that each internal space charge field component corresponds to the product of an odd function, presenting extreme values for ±k0, with Ĩr(kt) that corresponds to the autocorrelation function of the speckle intensity.

Fig. 2 (a) Intensity of a typical speckle pattern in the (x, y) spatial domain where the 1e2 half width of the speckle grains is σs = 0.21μm. (b) Intensity of the spatial frequency spectrum of the speckle field. (c) Modulus of the Fourier transform of the speckle intensity. In the spatial frequency domain, the axes are normalized by k0, the Debye screening wave number.
Fig. 3 (a) and (c) Modulus of the transverse components of the space charge electric field in the (kx, ky) spatial frequency domain. (b) and (d) Modulus the transverse components of the space charge electric field in the (x, y) spatial domain.

The crystallographic orientation of the BSO crystal used in [12

12. E. Benoit à la Guillaume, U. Bortolozzo, J. P. Huignard, S. Residori, and F. Ramaz, “Dynamic ultrasound modulated optical tomography by self-referenced photorefractive holography,” Opt. Lett. 38, 287–289 (2013). [CrossRef] [PubMed]

] is shown in Fig. 1. The light is incident on the plane (x, y) where the x axis is perpendicular to the plane (0,0,1) and the y axis is perpendicular to the plane (1,−1,0). In [12

12. E. Benoit à la Guillaume, U. Bortolozzo, J. P. Huignard, S. Residori, and F. Ramaz, “Dynamic ultrasound modulated optical tomography by self-referenced photorefractive holography,” Opt. Lett. 38, 287–289 (2013). [CrossRef] [PubMed]

], measurements of the angular dependency of the PR signal were performed with a photodiode placed in the far field of the PR crystal and that scanned the PR signal along the kx spatial frequencies where ky ≈ 0. For this spatial frequency range, the internal space charge field has only a component along the x axis (i.e. the scx(kt) component) and two birefringence axes appear, one parallel to the laboratory x axis, and one parallel to the y axis. The refractive indices found by the light polarized along these axes and propagating in the directions such that ky = 0, are n0 + Δnx and n0 + Δny where n0 is the linear refractive index of the BSO crystal and [13

13. P. Yeh, Introduction to Photorefractive Nonlinear Optics (John Wiley, 1993).

]
{Δnx(kx)=0Δny(kx)=12r41n03E˜scx(kx).
(4)
As scattered light is strongly depolarized, we emphasize that only the component of the speckle field polarized along the y axis reads the modulation of the refractive index Δny induced by the component scx of the internal space charge field. These results suggest that the x component of the speckle field provides no contribution to the PR signal. Then, in the experimental setup, the use of a polarizer oriented along the y axis at the output of the BSO crystal could improve the signal to noise ratio of the PR signal. For the y axis polarization considered in this paper, BSO exhibits both photoinduced birefringence and large optical activity at the green wavelength. In such conditions wave progation of an incident depolarized speckle beam is complex and its detailed analysis may be out of the scope of this paper. When taking account of the optical activity for linearly polarized plane waves, it leads to a reduction of the BSO holographic efficiency [16

16. J. A. Gómez, H. Lorduy Gómez, and Á. Salazar, “Novel procedure for the simultaneous determination of the Debye length and electro-optic coefficient for an optically active photorefractive Bi12SiO20 crystal,” Opt. Commun. 284, 460–466 (2011). [CrossRef]

].

Because the modulation of the refractive index is weak (10−5 to 10−6), the PR phase hologram induced by the speckle and read by the y polarized light can be expressed by :
Hy(x,y)=exp(i2πΔnyLλ)1i2πΔnyLλ
(5)
where L is the thickness of the hologram. Then, the y component of the output speckle field is given by:
Sryout(x,y)=Sryin(x,y)Hy(x,y).
(6)

Because of the small phase modulation induced by the hologram, the diffracted speckle is very similar to the reference speckle and the contribution of the PR signal in the output speckle is very weak. Then, the PR signal is obtained by subtracting the background level of light such that:
IPR(kx)=|S˜ryout(kx)|2|S˜ryin(kx)|2.
(8)

Fig. 4 Variation of the modulus of the x component of the space charge field (a) and of the PR signal (b) as a function of the normalized spatial frequency kxk0 (ky = 0) and of the mean size σs of the speckle grains. (c) Normalized PR signal as a function of the normalized spatial frequency kxk0 and the normalized half width of the gaussian envelop of the speckle spectrum σkk0. The black dotted curve depicts the optimized position of the detector that gives the higher PR signal as a fonction of σk.

Now, in order to modelize the ultrasound modulated optical tomography by self-referenced photorefractive holography reported in [12

12. E. Benoit à la Guillaume, U. Bortolozzo, J. P. Huignard, S. Residori, and F. Ramaz, “Dynamic ultrasound modulated optical tomography by self-referenced photorefractive holography,” Opt. Lett. 38, 287–289 (2013). [CrossRef] [PubMed]

], let us consider the case where an incident speckle tagged by a short US pulse, noted Stin, is diffracted by the hologram induced by the reference speckle Sr. Because the interaction between the short US pulse with the light propagating in the scattering medium leads to changes of the speckle pattern, the tagged speckle is transiently not perfectly matched with the complex phase hologram recorded in the whole volume of the BSO crystal. As a consequence, the level of the PR signal varies during the time of the US pulse.

In our simulations, the tagged speckle is modelised by the coherent superposition of the reference speckle Sr with a ”noise” noted Sn (i.e. a fully decorrelated speckle) so that the amplitude of the tagged speckle may be written in the (x, y) domain as:
Stin=γSn+1γSr,
(9)
where γ represents the ratio of the incident light interacting with the US pulse in the scatering medium. Then, the intensity of the tagged speckle is given by:
Itin=γIn+(1γ)Ir+2γ(1γ)𝔢{SnSr*}.
(10)
Because the noise speckle Sn is fully decorrelated with the reference speckle Sr, the mean value of the interference term between the two speckles is null. Figure 5 shows the typical result of the interference between two speckles fully decorrelated. Therefore, this term can be neglected when γ ≪ 1 so that the intensity of the tagged speckle is assumed to be the incoherent sum of the intensities of the two speckles. According to this assumption, the detected intensity of the tagged speckle that reads the PR hologram after US interaction can be written, in the spatial frequency domain, as :
|S˜tout|2γ|S˜nout|2+(1γ)|S˜rout|2.
(11)

Experimentally, the position of the photodiode is adjusted along the kx dimension to maximize the PR signal. Then, the measured AO signal is directly the intensity of the spectrum of the tagged speckle at this spatial frequency and the DC background corresponds to the intensity of the untagged speckle measured at the same spatial frequency. Hence, we will define the relative AO signal as :
RAO=ΔkD|S˜tout|2d2kΔkD|S˜rout|2d2kΔkD|S˜rout|2d2k
(12)
where ΔkD denotes the integration of the intensity of the spectrum of the diffracted speckle field over the spatial frequency bandwidth ΔkD of the photodiode. For numerical calculation, the mean radius of the speckle grains in the (x, y) is adjusted to 0.21 μm (i.e. the Debye screening length). Figure 6(a) represents the typical shape of the intensity of the spatial frequency spectrum of a tagged speckle and the two yellow squares symbolise the optimized position and the area of the detector centered on the spatial frequencies kx=±k02 (see Fig. 4(b)). For these two positions of the photodiode and using Eq. (12), we calculate the variation of the relative AO signals as a function of the level γ of the ”noise” in the tagged speckle. Assuming that the scattered light totally filled the volume of the scattering medium, the maximum value taken by γ is determined very approximately to 10−3 by calculating the ratio between the focusing volume of the US pulse (∼ 5mm3) and the total volume of the scattering medium (< 403 mm3). Figure 6(b) gives the variation of the relative AO signals, respectively noted RAO+ and RAO when the detector is centered on +k02 or k02, as a function of the level of noise in the tagged speckle. Because of the small number of speckle grains in the area of the simulated detector, the curves correspond to the AO signals averaged over few tens of numerical realizations. In agreement with the shape of the PR signal given by Fig. 4(b) and Eq. (11), the relative AO signal measured around +k02 and k02 respectively decreases and increases linearly, when the level of noise increases.

Fig. 5 (a) and (b) intensities in the (x, y) domain of the reference speckle and the fully decorrelated noise speckle. (c) Real part of the interference term between the reference and the noise speckles.
Fig. 6 (a) Intensity of the spatial frequency spectrum of a tagged speckle. The two yellow squares represent the detector area in the (kx, ky) domain when it is centered respectively on the spatial frequencies kx=±k02. (b) Amplitude of the AO signals as a function of the level γ of noise in the tagged speckle for the two positions of the detector.

All these results give a satisfactory quantitative interpretation of the experimental results reported in [12

12. E. Benoit à la Guillaume, U. Bortolozzo, J. P. Huignard, S. Residori, and F. Ramaz, “Dynamic ultrasound modulated optical tomography by self-referenced photorefractive holography,” Opt. Lett. 38, 287–289 (2013). [CrossRef] [PubMed]

]. However, the developed model mainly outlines the optimal values of the speckle grain size and of the detector position and, for the moment, does not permit to quantify the holographic efficiency and the AO signal dynamic range. In future work, several experimental parameters, such as fraction of tagged photons, beams polarization, light collection efficiency on the detector need to be carefully considered in order to refine amplitude consistency between the model and experiment.

3. Conclusion

The self referenced wavefront acousto-optic imaging technique has been analysed in the condition where a single speckle field is projected on a PR crystal. In these experiments, no reference beam is applied and the incident speckle creates a complex space charge field inducing a phase volume hologram in the BSO. The model leads to determine the parameters controling the efficiency of the hologram. We show that the PR signal efficiency is maximized for a spatial frequency that depends on the crystal Debye screening wave number, the width of the spatial frequency spectrum of the speckle but also on the angular aperture of the detector. It results that there is an optimum position of the photodetector and an optimum size of the speckle grains to detect the speckle pattern in presence of the tagged photons in an acousto-optic imaging experiment. The numerical simulations agree well with the experimental results previously reported. The method is robust and easy to implement in comparison with conventional holography. It can be applied with other types of nonlinear media in particular operating in the near IR region for acousto-optic imaging in highly scattering biological tissues and in turbid media and vibrometry.

Acknowledgments

This work was supported by the LABEX WIFI (Laboratory of Excellence within the French Program Investment for the Future) under references ANR-10-LABX-24 and ANR-10-IDEX-0001-02 PSL*, the ANR project under the name ICLM (Coherent Imaging of Multi-scattered Light, ANR-2011-BS0417) and the Conseil Régional de Franche-Comté. Computations have been performed on the supercomputer facilities of the Mésocentre de calcul de Franche–Comté.

References and links

1.

S. R. Arridge, “Optical tomography in medical imaging,” Inverse Probl. 15, R41–R93 (1999). [CrossRef]

2.

A. Bratchenia, R. Molenaar, T. G. van Leeuwen, and R. P. H. Kooyman, “Acousto-optic-assisted diffuse optical tomography,” Opt. Lett. 36, 1539–1541 (2011). [CrossRef] [PubMed]

3.

L. Wang, S. L. Jacques, and X. Zhao, “Continuous-wave ultrasonic modulation of scattered laser light to image objects in turbid media,” Opt. Lett. 20, 629–631 (1995). [CrossRef] [PubMed]

4.

G. Rousseau, A. Blouin, and J.-P. Monchalin, “Ultrasound modulated optical imaging using a high-power pulsed laser and a double-pass confocal Fabry-Perot interferometer,” Opt. Lett. 34, 3445–3447 (2009). [CrossRef] [PubMed]

5.

X. Xu, S.-R. Kothapalli, H. Liu, and L. V. Wang, “Spectral hole burning for ultrasound-modulated optical tomography of thick tissue,” J. Biomed. Opt. 15, 066018 (2010). [CrossRef]

6.

M. Gross, P. Goy, and M. Al-Koussa, “Shot-noise detection of ultrasound-tagged photons in ultrasound-modulated optical imaging,” Opt. Lett. 28, 2482–2484 (2003). [CrossRef] [PubMed]

7.

E. Benoit à la Guillaume, S. Farahi, E. Bossy, M. Gross, and F. Ramaz, “Acousto-optical coherence tomography with a digital holographic detection scheme,” Opt. Lett. 37, 3216–3218 (2012). [CrossRef] [PubMed]

8.

A. Lev and B. Sfez, “In vivo demonstration of the ultrasound-modulated light technique,” J. Opt. Soc. Am. A 20, 2347–2354 (2003). [CrossRef]

9.

S. Farahi, E. Benoit à la Guillaume, A. A. Grabar, J.-P. Huignard, and F. Ramaz, “Time resolved three-dimensional acousto-optic imaging of thick scattering media,” Opt. Lett. 37, 2754–2756 (2012). [CrossRef] [PubMed]

10.

M. Lesaffre, F. Jean, F. Ramaz, A. C. Boccara, P. Delaye, and G. Roosen, “In situ monitoring of the photorefractive response time in a self-adaptive holography setup developed for acousto-optic imaging,” Opt. Express 15, 1030–1042 (2007). [CrossRef] [PubMed]

11.

A. A. Kamshilin, T. Jaaskelainen, and Y. N. Kulchin, “Adaptive correlation filter for stabilization of interference fiber optic sensors,” Appl. Phys. Lett. 73, 705–707 (1998). [CrossRef]

12.

E. Benoit à la Guillaume, U. Bortolozzo, J. P. Huignard, S. Residori, and F. Ramaz, “Dynamic ultrasound modulated optical tomography by self-referenced photorefractive holography,” Opt. Lett. 38, 287–289 (2013). [CrossRef] [PubMed]

13.

P. Yeh, Introduction to Photorefractive Nonlinear Optics (John Wiley, 1993).

14.

O. Daniel, J.-M. C. Jonathan, and G. Roosen, “Photorefractrive effect in the Fourier plane,” Opt. Mater. 4, 294–298 (1995). [CrossRef]

15.

O. Daniel, A. Stelmach, J.-M. C. Jonathan, and G. Roosen, “Whole-beam method analysis of photorefractive effect in correlators,” Opt. Commun. 113, 559–567 (1995). [CrossRef]

16.

J. A. Gómez, H. Lorduy Gómez, and Á. Salazar, “Novel procedure for the simultaneous determination of the Debye length and electro-optic coefficient for an optically active photorefractive Bi12SiO20 crystal,” Opt. Commun. 284, 460–466 (2011). [CrossRef]

17.

J. W. Goodman, Laser Speckle and Related Phenomena (Springer, 1975).

OCIS Codes
(120.6160) Instrumentation, measurement, and metrology : Speckle interferometry
(190.5330) Nonlinear optics : Photorefractive optics
(110.0113) Imaging systems : Imaging through turbid media
(170.1065) Medical optics and biotechnology : Acousto-optics

ToC Category:
Imaging Systems

History
Original Manuscript: January 29, 2014
Revised Manuscript: March 13, 2014
Manuscript Accepted: April 15, 2014
Published: April 25, 2014

Virtual Issues
Vol. 9, Iss. 7 Virtual Journal for Biomedical Optics

Citation
Fabrice Devaux, Jean-Pierre Huignard, and François Ramaz, "Modelization and optimized speckle detection scheme in photorefractive self-referenced acousto-optic imaging," Opt. Express 22, 10682-10692 (2014)
http://www.opticsinfobase.org/oe/abstract.cfm?URI=oe-22-9-10682


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References

  1. S. R. Arridge, “Optical tomography in medical imaging,” Inverse Probl. 15, R41–R93 (1999). [CrossRef]
  2. A. Bratchenia, R. Molenaar, T. G. van Leeuwen, R. P. H. Kooyman, “Acousto-optic-assisted diffuse optical tomography,” Opt. Lett. 36, 1539–1541 (2011). [CrossRef] [PubMed]
  3. L. Wang, S. L. Jacques, X. Zhao, “Continuous-wave ultrasonic modulation of scattered laser light to image objects in turbid media,” Opt. Lett. 20, 629–631 (1995). [CrossRef] [PubMed]
  4. G. Rousseau, A. Blouin, J.-P. Monchalin, “Ultrasound modulated optical imaging using a high-power pulsed laser and a double-pass confocal Fabry-Perot interferometer,” Opt. Lett. 34, 3445–3447 (2009). [CrossRef] [PubMed]
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