Source: http://proxy.osapublishing.org/ol/abstract.cfm?uri=ol-41-5-1006
Timestamp: 2019-04-24 18:53:09+00:00

Document:
The idea of a method of cost-effective upgrades from an acoustic resolution photoacoustic microscope to a triple-modality imaging system is validated using phantoms. The newly developed experimental setup is based on a diode pumped solid state laser coupled to a fiber bundle with a spherically focused polyvinylidene fluoride detector integrated into the center of a ring shaped optical illuminator. Each laser pulse illuminating the sample performs two functions. While the photons absorbed by the sample provide a measurable optoacoustic (OA) signal, the photons absorbed by the detector provide the measurable diffuse reflectometry (DR) signal from the sample and the probing ultrasonic (US) pulse. At a 3 mm imaging depth, the axial resolution of the OA/US modalities is 38 μm/26 μm, while the lateral resolution of the DR/OA/US modalities is 3.5 mm/50 μm/35 μm. The maximum acquisition rate of the trimodal DR/OA/US A-scans is 2 kHz.
P. Beard, Interface Focus 1, 602 (2011).
V. Ntziachristos, Nature Methods 7, 603 (2010).
L. V. Wang and S. Hu, Science 335, 1458 (2012).
A. Taruttis and V. Ntziachristos, Nat. Photonics 9, 219 (2015).
M. Omar, D. Soliman, J. Gateau, and V. Ntziachristos, Opt. Lett. 39, 3911 (2014).
H. F. Zhang, K. Maslov, G. Stoica, and L. V. Wang, Nat. Biotechnol. 24, 848 (2006).
C. Xu, P. D. Kumavor, A. Aguirre, and Q. Zhu, J. Biomed. Opt. 17, 0612131 (2012).
M. Jaeger, K. Gashi, H. G. Akarçay, G. Held, S. Peeters, T. Petrosyan, S. Preisser, M. Gruenig, and M. Frenz, Photon. Lasers Med. 3, 343 (2014).
R. Bouchard, O. Sahin, and S. Emelianov, IEEE Trans. Ultrason. Ferroelectr. Freq. Control 61, 450 (2014).
F. Gao, X. Feng, and Y. Zheng, Appl. Phys. Lett. 104, 213701 (2014).
G. Wurzinger, R. Nuster, N. Schmitner, S. Gratt, D. Meyer, and G. Paltauf, Biomed. Opt. Express 4, 1380 (2013).
J. Xia, C. Huang, K. Maslov, M. A. Anastasio, and L. V. Wang, Opt. Lett. 38, 3140 (2013).
M. Jaeger, D. Harris-Birtill, A. Gertsch, E. O’Flynn, and J. Bamber, J. Biomed. Opt. 17, 066007 (2012).
P. Subochev, A. Katichev, A. Morozov, A. Orlova, V. Kamensky, and I. Turchin, Opt. Lett. 37, 4606 (2012).
P. Subochev, I. Fiks, M. Frenz, and I. Turchin, Laser Phys. Lett. 13, 025605 (2016).
K. Zell, J. Sperl, M. Vogel, R. Niessner, and C. Haisch, Phys. Med. Biol. 52, N475 (2007).
P. Di Ninni, Y. Bérubé-Lauzière, L. Mercatelli, E. Sani, and F. Martelli, Appl. Opt. 51, 7176 (2012).
G. Diebold, T. Sun, and M. Khan, Phys. Rev. Lett. 67, 3384 (1991).
Y. Hou, S. Ashkenazi, S.-W. Huang, and M. O’Donnell, IEEE Trans. Ultrason. Ferroelectr. Freq. Control 54, 682 (2007).
V. P. Zharov and V. S. Letokhov, Laser Optoacoustic Spectroscopy (Springer, 2013), Vol. 37.
D. Bergström, J. Powell, and A. Kaplan, J. Appl. Phys. 101, 113504 (2007).
M. Jaeger, S. Schüpbach, A. Gertsch, M. Kitz, and M. Frenz, Inverse Prob. 23, S51 (2007).
B. Cox, J. G. Laufer, S. R. Arridge, and P. C. Beard, J. Biomedical Optics 17, 0612021 (2012).
S. L. Jacques, J. Biomed. Opt. 15, 051608 (2010).
C. Xu, P. D. Kumavor, U. Alqasemi, H. Li, Y. Xu, S. Zanganeh, and Q. Zhu, J. Biomed. Opt. 18, 126006 (2013).
L. Xi, X. Li, L. Yao, S. Grobmyer, and H. Jiang, Med. Phys. 39, 2584 (2012).
A. Q. Bauer, R. E. Nothdurft, T. N. Erpelding, L. V. Wang, and J. P. Culver, J. Biomed. Opt. 16, 096016 (2011).
B. Ning, M. J. Kennedy, A. J. Dixon, N. Sun, R. Cao, B. T. Soetikno, R. Chen, Q. Zhou, K. Kirk Shung, and J. A. Hossack, Opt. Lett. 40, 910 (2015).
A. Mandelis, X. Guo, B. Lashkari, S. Kellnberger, and V. Ntziachristos, “Wavelength-modulated differential photoacoustic spectroscopy (WM-DPAS) for noninvasive early cancer detection and tissue hypoxia monitoring,” J. Biophoton., doi: 10.1002/jbio.201500131.
C.-W. Wei, T.-M. Nguyen, J. Xia, B. Arnal, E. Y. Wong, I. M. Pelivanov, and M. O’Donnell, IEEE Trans. Ultrason. Ferroelect. Freq. Control 62, 319 (2015).
Fig. 1. Experimental setup for OA/US/DR imaging, all bars are 5 mm. (a) Photograph of the scanning OA head; (b) ferrule containing the outputs of 70 fibers for optical illumination of the object with the hole for the PVDF detector; (c) spherically focused PVDF optoacoustic detector; (d) schematic of the experimental setup and the axial geometry of the optoacoustic focus; (e)–(g) lateral geometry of optical illumination, measured at different depths in water.
Fig. 2. Typical temporal DR/OA/US signals acquired from the OA A-scan of the phantom. (a) DR signal from the light-scattering background made of the water solution of 2% agar and 0.5% lipofundin; (b) OA A-line signal from the 50 μm copper wire located at the focus; (c) US A-line signal from 50 μm copper wire located at the focus.
Fig. 3. Resolution of the DR/OA/US modalities. (a) photograph of the agar phantom with the edge of the aluminum foil oriented along the Y axis; (b), (c) the OA/US axial profiles of the 10 μm aluminum foil acquired from the same A-scan, and their Gaussian fits; (d)–(f) the DR/OA/US MIP signals profiling the edge of the aluminum foil in the lateral direction and their fits by the integral of the Gaussian function.
Fig. 4. Results of DR/OA/US imaging of the phantom. (a) photograph of the agar phantom containing seven copper wires, the injection of lipofundin is marked by the white arrow, and the injection of black ink is marked by a yellow arrow; (b) MIP DR image; (c), (d) MIP OA images before and after the reconstruction; (e), (f) MIP US images before and after reconstruction .

References: V. 
 V. 
 V. 
 V. 
 V. 
 V. 
 V. 

V. 
 V. 
 V. 
 V.