BODIPY derivatives as molecular photoacoustic contrast agents
-
Upload
independent -
Category
Documents
-
view
1 -
download
0
Transcript of BODIPY derivatives as molecular photoacoustic contrast agents
BODIPY derivatives as molecular photoacoustic contrast agents
Samir Laoui,1 Seema Bag,2 Olivier Dantiste,1 Mathieu Frenette,2 Maryam Hatamimoslehabadi,1
Stephanie Bellinger-Buckley,2 Jen-Chieh Tseng,3 Jonathan Rochford,2† Chandra Yelleswarapu1* 3Lurie Family Imaging Center, Dana-Farber Cancer Institute, 450 Brookline Avenue, Boston,
MA 02215. 2 Department of Chemistry, 1 Department of Physics, University of Massachusetts
Boston, 100 Morrissey Blvd, Boston, MA 02125.
ABSTRACT
Photoacoustic imaging (PAI) is emerging as a key in vivo imaging technique. Endogenous contrast agents alone are
insufficient to obtain high contrast images necessitating a need for synthetic exogenous contrast agents. In recent years
a great deal of research has been devoted to the development of nanoparticle based contrast agents with little effort on
molecular systems. Here we report on the design and evaluation of BODIPY inspired molecular photoacoustic contrast
agents (MPACs). Through chemical modification of the established BODIPY fluorophore, increasing its vibrational
freedom and appending with non-emissive functionalities, it is demonstrated that the S0S1 absorbed excitation energy is redirected towards a nonradiative excited-state decay pathway. Optical and photoacoustic characterization
of the modified BODIPY MPACs demonstrates a stronger photoacoustic signal compared to the corresponding
fluorescent BODIPY probes.
Keywords: Molecular contrast agents, Fluorescence quenching, Photoacoustic imaging, Bodipy, Nonlinear
photoacoustics
† [email protected], phone 1 617-6133; fax 1 617-287-6030. * [email protected], phone 1 617-287-6063; fax 1 617-287-6053.
INTRODUCTION
Cancer is the most prevalent disease throughout the world. For successful diagnosis and treatment, a complete
understanding of cancer tumor growth is necessary. Photoacoustic imaging (PAI; aka photoacoustic tomography) is
emerging as a key in vivo imaging technique to aid in the understanding of cancer growth by providing tumor location
and metabolic activity [1, 2]. It represents a best of both worlds approach, combining high optical contrast with low
scattering of ultrasound in biological media. PAI is based on the photoacoustic effect, i.e. the conversion of optical
energy into acoustic energy. When laser pulses are incident on biological tissue, photons of appropriate energy may
be absorbed by endogenous chromophores, e.g. melanian and hemoglobin, and nonradiative decay takes place with
the release of localized heat. This produces a small temperature rise, characterized by the specific heat capacity of the
medium leading to a volumetric thermal expansion of the optical interaction region. Usually the optical absorption of
endogenous contrast agents show a substantial PA response to allow vascular tissue imaging. In many scenarios
however, such as the detection of early stage tumors, an endogenous contrast agent alone is insufficient to provide
enough information. In these cases, optimized exogenous contrast agents were employed to provide better
signal/contrast for photoacoustic imaging [3-10]. However, in order to capture high resolution images of a tumor in
deep tissue, the availability of an effective contrast agent is essential.
Nanomaterials have attracted much attention as contrast agents because they can be engineered in various sizes and
shapes to generate high aspect ratio and tunable optical, magnetic and biological properties [8, 11-22]. Gold
nanostructures (nanoparticles, nanoshells, nanocages, nanorods etc.) are being extensively investigated for biomedical
applications in view of their favorable photonic properties and scope of functionalization, e.g. bioconjugation [18, 23-
33]. Gold nanorods in particular have been targeted as potential contrast agents for PAI due to their strong tunable
NIR absorption and enhancement of their photothermal properties which arise from the plasmon resonance effect [34,
35]. For example, near-infrared (NIR) absorbing gold nanocages have been successfully studied as a new class of
tracers for photoacoustic sentinel lymph node mapping on a rat model [36]. Furthermore, single-walled carbon
Reporters, Markers, Dyes, Nanoparticles, and Molecular Probes for Biomedical Applications VI, edited by Samuel Achilefu, Ramesh Raghavachari, Proc. of SPIE Vol. 8956, 895609 · © 2014
SPIE · CCC code: 1605-7422/14/$18 · doi: 10.1117/12.2040057
Proc. of SPIE Vol. 8956 895609-1
Downloaded From: http://spiedigitallibrary.org/ on 07/17/2014 Terms of Use: http://spiedl.org/terms
nanotubes have also shown promise as molecular contrast agents for the photoacoustic imaging of tumors when
functionalized with cyclic Arg-Gly-Asp (RGD) peptides and PEGylated dendrons[9, 37, 38]. In contrast to the diverse
nature of nanoparticulate based PA contrast agents studied to date, studies of molecular based systems are rare and
are typically based upon commercially available NIR fluorescent dyes [39-46]. For example, in vivo PAI studies on
indocyanine green and its derivatives are rare and have been mostly limited to non-specific investigations of vascular
lymph tissue or specific targeting of integrin in U87 xenografts [47]. The indocyanine green derivative IRDye800-
NHS has been mostly studied due to its commercial availability, strong NIR absorption (max = 800 nm, = 2.7 x 105
M-1 cm-1), poor fluorescence quantum yield (Fl = 0.10) and N-hydrosuccinimide functionality allowing for protein
conjugation via lysine residues [48]. PAI using the rhodamine based AlexaFluor750 dye has also been reported
recently with some success; however it remains that the only option currently available for PAI contrast agents is to
choose existing NIR absorbing fluorescent probes with the hope that they may generate a substantial PA response.
The caveat here is that fluorophores such as AlexaFluor750 have been designed with an optimized fluorescence
emission response and are not anticipated to generate a substantial photoacoustic response. The limited studies of
molecular based PA contrast agents is in stark contrast to the large catalogues of commercially available contrast
agents available today for fluorescence imaging applications. Thus there exists an urgent need to develop a broader
catalogue of PA contrast agents with tailored absorption profiles, improved conjugation strategies for targeted
imaging, and of course an optimized PA response.
In this study a series of molecular based photoacoustic contrast agents (MPACs) are presented whose design is inspired
by the well-established 4,4-Difluoro-4-bora-3a,4a-diaza-s-indacene (BODIPY) fluorophore. BODIPY is well
documented for its use as a fluorescence probe for in vivo imaging due to its strong, sharp absorption in the visible
region (max = 500 nm, = 1.20 x 105 M-1 cm-1), small Stokes shift (392 cm-1) and large fluorescence quantum yield
(fl ~ 0.9). However, by increasing the vibrational freedom of the BODIPY molecule and appending non-emissive
fluorescence quenching functionalities in conjugation with BODIPY it is here demonstrated that the S1 excited-state
energy is redirected towards a nonradiative decay pathway which significantly increases the photoacoustic response.
METHODOLOGY
To the best of our knowledge, there are no prior reports in the scientific literature which have investigated the PA
properties of any BODIPY system. This is unsurprising however given the reputation of BODIPY as an efficient
fluorophore whose unique photophysical properties make it unsurpassed as an in vivo fluorescence probe. As such we
take advantage of its highly attractive absorption properties but, by way of understanding its structure-function
properties, have successfully redirected its S1 excited-state energy towards a nonradiative relaxation pathway
contributing significantly towards a desired PA response.
The PA response of any system is determined by a photoinduced change in enthalpy (H) of that system from its
equilibrium thermodynamic state giving rise to heat dissipation and volume expansion (V). These enthalpic and
volumetric changes can be described at the molecular level by both internal (structural/electronic) and external
(environmental) factors, i.e. molecular vibration and solvent/ion reorganization energies, respectively. Having no
control over the environmental factors in vivo our basic design principle is to target structures capable of undergoing
significant structural and/or electronic distortion upon population of their S1 excited states with low energy visible
radiation. Relaxation of the metastable excited-state to the S0 singlet ground-state for the basic meso-aryl-1,3,5,7-
tetramethyl-BODIPY molecule 1 (Fig. 1) occurs predominantly via direct S0S1 radiative decay due to the highly
rigid conformation of its atomic scaffold. By taking advantage of Knoevanagel based -extension strategies at the 1
and 7 positions of 1 with mono- or bis-styryl functionalization, nonradiative decay pathways can be accessed from the
S1 excited-state by increasing the structural flexibility and degrees of freedom for the molecule; in effect taking a
detour en-route to the S0 ground state via the lesser travelled vibrational pathways.
Proc. of SPIE Vol. 8956 895609-2
Downloaded From: http://spiedigitallibrary.org/ on 07/17/2014 Terms of Use: http://spiedl.org/terms
Figure 1. Structural representation of the reference BODIPY system 1, the extended bis-styryl p-methoxyphenyl (2) and bis-
styryl ferrocenyl BODIPY (3) constrast agents.
On comparing the organic MPACs 1 and 2 successive extension of the -system by introduction of the organic p-
methoxy styrylbenzene substituents gives rise to a 140 nm red-shift in the electronic absorption maximum from 500
(5.45 x105 M-1 cm-1) to 640 nm (4.34 x105 M-1 cm-1) with a slight increase in molar extinction coefficient for
the lowest energy * electronic transition. Accordingly, there is a comparable red-shift of 144 nm observed in the
fluorescence emission spectra (Figure 2, Table 1). The comparable oscillator strengths of this S0S1 electronic
excitation for 1 and 2, and minimal broadening of their full-width-half-maxima (fwhm = 40 cm-1), indicates little
divergence between their ground and excited state geometries even in the presence of both styryl -conjugated groups
for 2. In fact, the non-styryl BODIPY 1 dye displays a lower fluorescence quantum yield (Fl = 0.306) relative to
compound 2 (Fl = 0.719), most probably due to localization of the S0 and S1 electronic wavefunctions in close
proximity to the rotating meso-aryl substituent (Fig. 2b). On comparing the organic MPACs 2 and 3, substitution with
the organometallic, electron rich, ferrocenyl substituent a further red-shift is observed with a two-fold drop in molar
extinction coefficient (max = 687 nm; 2.51 x105 M-1 cm-1). This correlates with a dramatic five-fold increase of
the fwhm for the lowest energy (S0S1) d*, i.e. metal-to-ligand charge transfer (MLCT), absorption band relative
to the (S0S1) *, electronic absorption band for 2. This peak broadening is highly significant as it indicates an
increased Boltzmann population of vibrational levels in the S1 excited-state, no doubt as a consequence of increased
vibrational freedom upon introduction of the substituents. Such extensive broadening is characteristic of transition
metal d* charge transfer (MLCT) transitions. As anticipated, 3 displays zero fluorescence signal due to strong
vibronic-coupling of the BODIPY S1 excited-state with the ferrocenyl based MLCT excited state. Ferrocene
complexes are known to undergo rapid nonradiative decay via ligand field electronic excited states at the iron center.
Proc. of SPIE Vol. 8956 895609-3
Downloaded From: http://spiedigitallibrary.org/ on 07/17/2014 Terms of Use: http://spiedl.org/terms
Figure 2. (a) UV/Vis electronic absorption spectra for MPACs 1, 2 and 3 and (b) fluorescence emission spectra for MPACs 1 and
2 recorded at room temperature in spectrophotometric grade acetonitrile.
Table 1. UV/Vis electronic absorption and fluorescence emission data for MPACs 1, 2 and 3 recorded at room temperature in
spectrophotometric grade acetonitrile (all fluorescence samples were thoroughly degassed with argon prior to measurement).
a estimated following deconvolution of MLCT absorption bands.
To gain further insight into the electronic structure of these systems preliminary computational investigations were
conducted to ascertain the extent of -conjugation in these complex systems. Computational analysis was conducted
using the density functional theory B3LYP functional with 6-31g* (H, B, C, N, O, F) and LANL2DZ (Fe) basis sets.
Due to space considerations only the highest occupied (HOMO) and lowest unoccupied (LUMO) frontier molecular
orbitals are shown in Figure 3. Trends in the UV/Vis absorption and fluorescence emission spectra can be better
understood by analysis of the frontier orbitals and their respective energies (viz. electrochemical analysis) with the
HOMOLUMO band-gaps decreasing upon increased conjugation via the p-methoxystyrylbenzene substituents in the
1 and 7 positions of the BODIPY ring. Delocalization of electron density from the ferrocene unit onto the styryl-
BODIPY system is clearly evident also confirming the MLCT nature of the low energy electronic transitions in 3.
UV/Vis (max, nm)
(x105 M-1 cm-1) fwhm (cm-1)
emission
(max, nm)
Stokes shift
(cm-1) fl
1 310 (0.48), 364 (0.34), 500 (5.45) 806 510 392 0.306
2 318 (0.93), 368 (2.70), 590 (1.54), 640 (4.34) 813 654 334 0.719
3 280 (1.12), 344 (2.60), 559 (1.22), 687 (2.51) 3929, 2223 a ~ ~ ~
450 500 550 600 650 700 7500.0
0.2
0.4
0.6
0.8
1.0 1 BODIPY
2 (MeO)2BODIPY
Flu
ore
scen
ce Q
ua
ntu
m Y
ield
(
Fl)
Wavelength (nm)
300 400 500 600 700 800 900
0
1
2
3
4
5
1 BODIPY
2 (MeOPh)2BODIPY
3 Fc2BODIPY
(x
10
4 M
-1 c
m-1)
Wavelength (nm)
Proc. of SPIE Vol. 8956 895609-4
Downloaded From: http://spiedigitallibrary.org/ on 07/17/2014 Terms of Use: http://spiedl.org/terms
LUMO
-1.49 V
2.23 eV
0.74V
LUMO
-1.30 V
fi1.67 eV
0.37 V
1 2
LUMO
-1.38 V
1.45 eV
0.07 V
2.01 eV
0.63 V
Figure 3. Computational analysis using the density functional theory B3LYP functional with 6-31g* (H, B, C, N, O, F) and
LANL2DZ (Fe) basis sets for MPACs 1, 2 and 3. Energy levels are estimated on the basis of electrochemical data.
An important observation here is that delocalization or increase vibrational freedom alone is not sufficient enough
to quench BODIPY fluorescence; while extended -conjugation is observed to increase the fluorescence quantum
yield upon comparison of 1 and 2, energy level alignment of the ferrocenyl redox centres in 3 is deemed responsible
for complete quenching of the BODIPY fluorescence by a photoinduced electron-transfer event.[49]
Photoacoustic characterization of contrast agents: For these studies we used our recently developed photoacoustic
z-scan technique [50]. A schematic of the experimental setup is shown in Scheme 1. A frequency doubled Nd:YAG
laser (exc = 532 nm) is focused onto the sample with a 20 cm focal length lens. The sample is placed in a 2 mm quartz
cuvette and is mounted in a custom made cell that contains water for ultrasound coupling. As the visible laser pulse is
incident on the sample, some of the energy delivered is absorbed by the HOMOLUMO electronic transition described
above, and subsequently dissipated as a mixture of fluorescence and/or heat, depending upon the sample in question.
Heat production (H) by the excited state molecule produces pressure transients and thus wideband ultrasonic
Proc. of SPIE Vol. 8956 895609-5
Downloaded From: http://spiedigitallibrary.org/ on 07/17/2014 Terms of Use: http://spiedl.org/terms
Nd: YAG Laser1. =532 nm
Lensf =20cm
1
v
Sample>
Water
Photoacoustictransducer
r--,
optical
Detector
emission in its local environment. The ultrasonic waves (PA signal) are then detected using a 10 MHz focused water
immersion transducer. The sample cell is placed at 45° with respect to the incident laser beam. The whole system is
mounted on a XYZ translation stage and aligned carefully so that the PA signal collected by the transducer is optimum.
The sample is then translated along the direction of the laser beam in discrete steps such that the focal region (on either
side of the focal point) of the beam scans the sample along the Z-direction. Concurrently the laser beam transmitted
through the samples is measured using a photodiode. This arrangement enables simultaneous monitoring of both
optical transmission and photoacoustic response of the sample under investigation.
Scheme 1. An illustration of the experimental assembly for conducting Z-scan experiments to elucidate MPACs PA response.
The experimental setup was initially optimized with standard nonlinear absorbing materials such as
zinc(II)phthalocyanine and C60-fullerene. The optical and photoacoustic response of MPACs 1, 2 and 3 were then
investigated in acetonitrile with a uniform optical density of 0.5 at 532 nm. The reference BODIPY system 1 shows
very weak absorption at 532 nm and as such a high concentration of sample was required. In any case, due to the
favored fluorescence response of this system a negligible photoacoustic response was observed. Upon excitation with
the 532 nm laser pulse a strong fluorescence response was also evident for 2. As stated above any fluorescence
response was completely absent for the ferrocenyl derivative 3. A plot of PA response vs. laser intensity for selected
MPACs is presented in Figure 4. In the case of 2, an estimated 28.1 % of the excited state energy is available for
contribution to a PA response (Fl = 0.719), as least in a linear optical absorption regime. The bis-ferrocenyl derivative
3 shows zero fluorescence response which correlates to an almost 4-fold increase in the PA signal relative 2.
Significantly, for 3 the PA signal displays a linear increase with increasing laser flux. This is in stark contrast to
MPACs 2 (MeOPh)2BODIPY which shows evidence of a non-linear absorption which saturates beyond ~1x1012 J/m2.
Proc. of SPIE Vol. 8956 895609-6
Downloaded From: http://spiedigitallibrary.org/ on 07/17/2014 Terms of Use: http://spiedl.org/terms
120 -
100 -
8 0 -
6 0 -
40 -
.
20-
0
5-Fc2BODIPY3{AI eOPh)=BO DIP Y
.. ...:..- *: 'A'#+t' ,
.....
,
.-
0.........................
0 1 2
Intenstiy (x 101" J/m2)
Figure 5. Plot of PA response vs. laser intensity for MPACs (MeOPh)2BODIPY and Fc2BODIPY recorded in methanol
by the Z-scan technique with optical densities of 0.5.
CONCLUSION
In conclusion we have successfully designed and characterized BODIPY inspired molecular photoacoustic contrast
agents (MPACs). By chemically modifying -extensions at the 1 and 7 positions of 1 with styryl methoxyphenyl or styryl ferrocene systems, the fluorescence quantum yield was tuned from 0.859 to nil. Concurrently the photoacoustic
response is amplified ultimately achieving a four-fold increase.
REFERENCES
[1] L. V. Wang, and S. Hu, “Photoacoustic tomography: in vivo imaging from organelles to organs,” Science,
335(6075), 1458-62 (2012).
[2] L. Xiang, B. Wang, L. Ji et al., “4-D photoacoustic tomography,” Sci Rep, 3, 1113 (2013). [3] L. Li, H. F. Zhang, R. J. Zemp et al., “Simultaneous imaging of a lacZ-marked tumor and microvasculature
morphology in vivo by dual-wavelength photoacoustic microscopy,” J Innov Opt Health Sci, 1(2), 207-215
(2008).
[4] P. C. Li, C. R. Wang, D. B. Shieh et al., “In vivo photoacoustic molecular imaging with simultaneous multiple
selective targeting using antibody-conjugated gold nanorods,” Opt Express, 16(23), 18605-15 (2008).
[5] K. H. Song, E. W. Stein, J. A. Margenthaler et al., “Noninvasive photoacoustic identification of sentinel
lymph nodes containing methylene blue in vivo in a rat model,” J Biomed Opt, 13(5), 054033 (2008).
[6] M. Pramanik, M. Swierczewska, D. Green et al., “Single-walled carbon nanotubes as a multimodal-
thermoacoustic and photoacoustic-contrast agent,” J Biomed Opt, 14(3), 034018 (2009).
[7] L. Au, J. Chen, L. V. Wang et al., “Gold nanocages for cancer imaging and therapy,” Methods Mol Biol,
624, 83-99 (2010). [8] X. Yang, E. W. Stein, S. Ashkenazi et al., “Nanoparticles for photoacoustic imaging,” Wiley Interdiscip Rev
Nanomed Nanobiotechnol, 1(4), 360-8 (2009).
[9] A. de la Zerda, Z. Liu, S. Bodapati et al., “Ultrahigh sensitivity carbon nanotube agents for photoacoustic
molecular imaging in living mice,” Nano Lett, 10(6), 2168-72 (2010).
[10] G. Luke, D. Yeager, and S. Emelianov, “Biomedical Applications of Photoacoustic Imaging with Exogenous
Contrast Agents,” Annals of Biomedical Engineering, 40(2), 422-437 (2012).
[11] J. A. Hubbell, and A. Chilkoti, “Nanomaterials for Drug Delivery,” Science, 337(6092), 303-305 (2012).
[12] M. A. Hahn, A. K. Singh, P. Sharma et al., “Nanoparticles as contrast agents for in-vivo bioimaging: current
status and future perspectives,” Anal Bioanal Chem, 399(1), 3-27 (2011).
Proc. of SPIE Vol. 8956 895609-7
Downloaded From: http://spiedigitallibrary.org/ on 07/17/2014 Terms of Use: http://spiedl.org/terms
[13] K. A. Homan, M. Souza, R. Truby et al., “Silver nanoplate contrast agents for in vivo molecular
photoacoustic imaging,” ACS Nano, 6(1), 641-50 (2012).
[14] H. Gong, R. Peng, and Z. Liu, “Carbon nanotubes for biomedical imaging: The recent advances,” Adv Drug
Deliv Rev, 65(15), 1951-63 (2013).
[15] G. P. Luke, A. Bashyam, K. A. Homan et al., “Silica-coated gold nanoplates as stable photoacoustic contrast
agents for sentinel lymph node imaging,” Nanotechnology, 24(45), 455101 (2013). [16] Y. Jin, “Multifunctional Compact Hybrid Au Nanoshells: A New Generation of Nanoplasmonic Probes for
Biosensing, Imaging, and Controlled Release,” Acc Chem Res, (2013).
[17] L. Wu, X. Cai, K. Nelson et al., “A Green Synthesis of Carbon Nanoparticle from Honey for Real-Time
Photoacoustic Imaging,” Nano Res, 6(5), 312-325 (2013).
[18] W. Li, P. K. Brown, L. V. Wang et al., “Gold nanocages as contrast agents for photoacoustic imaging,”
Contrast Media Mol Imaging, 6(5), 370-7 (2011).
[19] Z. Yuan, and H. Jiang, [Photoacoustic Tomography for Imaging Nanoparticles] Humana Press, 21 (2010).
[20] P. K. Jain, K. S. Lee, I. H. El-Sayed et al., “Calculated absorption and scattering properties of gold
nanoparticles of different size, shape, and composition: applications in biological imaging and biomedicine,”
The Journal of Physical Chemistry B, 110(14), 7238-7248 (2006).
[21] X. Yang, E. W. Stein, S. Ashkenazi et al., “Nanoparticles for photoacoustic imaging,” Wiley interdisciplinary
reviews: nanomedicine and nanobiotechnology, 1(4), 360-368 (2009). [22] Z. Liu, S. Tabakman, K. Welsher et al., “Carbon nanotubes in biology and medicine: in vitro and in vivo
detection, imaging and drug delivery,” Nano Res, 2(2), 85-120 (2009).
[23] C. Kim, E. C. Cho, J. Chen et al., “In vivo molecular photoacoustic tomography of melanomas targeted by
bioconjugated gold nanocages,” ACS Nano, 4(8), 4559-64 (2010).
[24] X. Liangzhong, X. Da, G. Huaimin et al., "Gold nanoshell-based photoacoustic imaging application in
biomedicine." 76-79.
[25] L. Rouleau, R. Berti, V. W. Ng et al., “VCAM-1-targeting gold nanoshell probe for photoacoustic imaging
of atherosclerotic plaque in mice,” Contrast Media Mol Imaging, 8(1), 27-39 (2013).
[26] H. Ju, R. A. Roy, and T. W. Murray, “Gold nanoparticle targeted photoacoustic cavitation for potential deep
tissue imaging and therapy,” Biomed Opt Express, 4(1), 66-76 (2013).
[27] Y. Wang, X. Xie, X. Wang et al., “Photoacoustic tomography of a nanoshell contrast agent in the in vivo rat brain,” Nano Lett, 4(9), 1689-1692 (2004).
[28] S. Mallidi, T. Larson, J. Tam et al., “Multiwavelength photoacoustic imaging and plasmon resonance
coupling of gold nanoparticles for selective detection of cancer,” Nano Lett, 9(8), 2825-2831 (2009).
[29] W. Lu, Q. Huang, G. Ku et al., “Photoacoustic imaging of living mouse brain vasculature using hollow gold
nanospheres,” Biomaterials, 31(9), 2617-2626 (2010).
[30] J. Chen, F. Saeki, B. J. Wiley et al., “Gold nanocages: bioconjugation and their potential use as optical
imaging contrast agents,” Nano Lett, 5(3), 473-477 (2005).
[31] P.-C. Li, C.-R. C. Wang, D.-B. Shieh et al., “In vivo Photoacoustic Molecular Imaging with Simultaneous
Multiple Selective Targeting Using Antibody-Conjugated Gold Nanorods,” Optics Express, 16(23), 18605-
18615 (2008).
[32] A. Agarwal, S. Huang, M. ODonnell et al., “Targeted gold nanorod contrast agent for prostate cancer
detection by photoacoustic imaging,” Journal of Applied Physics, 102(6), 064701-064701-4 (2007). [33] Q. Zhang, N. Iwakuma, P. Sharma et al., “Gold nanoparticles as a contrast agent for in vivo tumor imaging
with photoacoustic tomography,” Nanotechnology, 20(39), 395102 (2009).
[34] P.-C. Li, C.-W. Wei, C.-K. Liao et al., "Multiple targeting in photoacoustic imaging using bioconjugated
gold nanorods." 60860M-60860M-10.
[35] M. Eghtedari, A. Oraevsky, J. A. Copland et al., “High sensitivity of in vivo detection of gold nanorods using
a laser optoacoustic imaging system,” Nano Lett, 7(7), 1914-1918 (2007).
[36] K. H. Song, C. Kim, C. M. Cobley et al., “Near-infrared gold nanocages as a new class of tracers for
photoacoustic sentinel lymph node mapping on a rat model,” Nano Lett, 9(1), 183-8 (2009).
[37] A. De la Zerda, C. Zavaleta, S. Keren et al., “Carbon nanotubes as photoacoustic molecular imaging agents
in living mice,” Nat Nanotechnol, 3(9), 557-62 (2008).
[38] L. Xiang, Y. Yuan, D. Xing et al., “Photoacoustic molecular imaging with antibody-functionalized single-walled carbon nanotubes for early diagnosis of tumor,” Journal of Biomedical Optics, 14(2), 021008-021008-
7 (2009).
Proc. of SPIE Vol. 8956 895609-8
Downloaded From: http://spiedigitallibrary.org/ on 07/17/2014 Terms of Use: http://spiedl.org/terms
[39] S. Bhattacharyya, S. Wang, D. Reinecke et al., “Synthesis and evaluation of near-infrared (NIR) dye-
herceptin conjugates as photoacoustic computed tomography (PCT) probes for HER2 expression in breast
cancer,” Bioconjug Chem, 19(6), 1186-93 (2008).
[40] D. Razansky, C. Vinegoni, and V. Ntziachristos, “Multispectral photoacoustic imaging of fluorochromes in
small animals,” Opt Lett, 32(19), 2891-3 (2007).
[41] J. Koo, M. Jeon, Y. Oh et al., “In vivo non-ionizing photoacoustic mapping of sentinel lymph nodes and bladders with ICG-enhanced carbon nanotubes,” Phys Med Biol, 57(23), 7853-62 (2012).
[42] J. Zhong, S. Yang, X. Zheng et al., “In vivo photoacoustic therapy with cancer-targeted indocyanine green-
containing nanoparticles,” Nanomedicine (Lond), (2012).
[43] B. Wang, Q. Zhao, N. M. Barkey et al., “Photoacoustic tomography and fluorescence molecular tomography:
a comparative study based on indocyanine green,” Med Phys, 39(5), 2512-7 (2012).
[44] Y. Kohl, C. Kaiser, W. Bost et al., “Near-infrared dye-loaded PLGA nanoparticles prepared by spray drying
for photoacoustic applications,” Int J Artif Organs, 34(2), 249-52 (2011).
[45] C. Kim, K. H. Song, F. Gao et al., “Sentinel lymph nodes and lymphatic vessels: noninvasive dual-modality
in vivo mapping by using indocyanine green in rats--volumetric spectroscopic photoacoustic imaging and
planar fluorescence imaging,” Radiology, 255(2), 442-50 (2010).
[46] G. Kim, S. W. Huang, K. C. Day et al., “Indocyanine-green-embedded PEBBLEs as a contrast agent for
photoacoustic imaging,” J Biomed Opt, 12(4), 044020 (2007). [47] M. Li, J. Oh, X. Xie et al., “Simultaneous molecular and hypoxia imaging of brain tumors in vivo using
spectroscopic photoacoustic tomography,” PROCEEDINGS-IEEE, 96(3), 481 (2008).
[48] E. Baslé, N. Joubert, and M. Pucheault, “Protein Chemical Modification on Endogenous Amino Acids,”
Chemistry & biology, 17(3), 213-227 (2010).
[49] J. Rochford, A. D. Rooney, and M. T. Pryce, “Redox Control of meso-Zinc(II) Ferrocenylporphyrin Based
Fluorescence Switches,” Inorganic Chemistry, 46(18), 7247-7249 (2007).
[50] C. S. Yelleswarapu, and S. R. Kothapalli, “Nonlinear photoacoustics for measuring the nonlinear optical
absorption coefficient,” Opt Express, 18(9), 9020-5 (2010).
Proc. of SPIE Vol. 8956 895609-9
Downloaded From: http://spiedigitallibrary.org/ on 07/17/2014 Terms of Use: http://spiedl.org/terms