OSA's Digital Library

Biomedical Optics Express

Biomedical Optics Express

  • Editor: Joseph A. Izatt
  • Vol. 2, Iss. 1 — Jan. 1, 2011
  • pp: 80–88
« Show journal navigation

High speed multiphoton axial scanning through an optical fiber in a remotely scanned temporal focusing setup

Adam Straub, Michael E. Durst, and Chris Xu  »View Author Affiliations


Biomedical Optics Express, Vol. 2, Issue 1, pp. 80-88 (2011)
http://dx.doi.org/10.1364/BOE.2.000080


View Full Text Article

Acrobat PDF (1375 KB)





Browse Journals / Lookup Meetings

Browse by Journal and Year


   


Lookup Conference Papers

Close Browse Journals / Lookup Meetings

Article Tools

Share
Citations

Abstract

Simultaneous spatial and temporal focusing is used to acquire high speed (200Hz), chemically specific axial scans of mouse skin through a single-mode fiber. The temporal focus is remotely scanned by modulating the group delay dispersion (GDD) at the proximal end of the fiber. No moving parts or electronics are required at the distal end. A novel GDD modulation technique is implemented using a piezo bimorph mirror in a folded grating pair to achieve a large GDD tuning range at high speed.

© 2010 OSA

1. Introduction

Depth-resolved microscopy shows great promise in the fields of biology and medicine. The ability to optically scan through layers of cells makes available histological information that would otherwise be obtained only through tissue biopsy. Experiments in depth-resolved tissue spectroscopy and imaging have shown that confocal and multiphoton fluorescence and harmonic generation microscopy techniques can effectively be used in cancer detection and diagnostics [1

1. Y. Wu, P. Xi, J. Qu, T. H. Cheung, and M. Y. Yu, “Depth-resolved fluorescence spectroscopy of normal and dysplastic cervical tissue,” Opt. Express 13(2), 382–388 (2005). [CrossRef] [PubMed]

3

3. W. R. Zipfel, R. M. Williams, R. Christie, A. Y. Nikitin, B. T. Hyman, and W. W. Webb, “Live tissue intrinsic emission microscopy using multiphoton-excited native fluorescence and second harmonic generation,” Proc. Natl. Acad. Sci. U.S.A. 100(12), 7075–7080 (2003). [CrossRef] [PubMed]

]. Efforts have been made to incorporate these techniques into fiber probes for clinical application [4

4. R. Kiesslich, J. Burg, M. Vieth, J. Gnaendiger, M. Enders, P. Delaney, A. Polglase, W. McLaren, D. Janell, S. Thomas, B. Nafe, P. R. Galle, and M. F. Neurath, “Confocal laser endoscopy for diagnosing intraepithelial neoplasias and colorectal cancer in vivo,” Gastroenterology 127(3), 706–713 (2004). [CrossRef] [PubMed]

7

7. F. Helmchen, M. S. Fee, D. W. Tank, and W. Denk, “A miniature head-mounted two-photon microscope. high-resolution brain imaging in freely moving animals,” Neuron 31(6), 903–912 (2001). [CrossRef] [PubMed]

].

Scan speed is an important factor in in vivo microscopic imaging to reduce motion artifacts introduced by the sample movement. In a typical point-scanning depth-resolved microscope, the lateral dimensions are scanned using galvanometer mirror scanners at line rates of several kHz. Miniaturized MEMS scanners and piezo-electric scanners have been used for lateral scanning in miniature, flexible fiber probes [5

5. B. A. Flusberg, J. C. Jung, E. D. Cocker, E. P. Anderson, and M. J. Schnitzer, “In vivo brain imaging using a portable 3.9 gram two-photon fluorescence microendoscope,” Opt. Lett. 30(17), 2272–2274 (2005). [CrossRef] [PubMed]

7

7. F. Helmchen, M. S. Fee, D. W. Tank, and W. Denk, “A miniature head-mounted two-photon microscope. high-resolution brain imaging in freely moving animals,” Neuron 31(6), 903–912 (2001). [CrossRef] [PubMed]

]. The axial dimension in a typical microscope is scanned either by moving the sample relative to the output optics of the system or by moving a lens within the optical system. Because of the necessary movement of a bulk object, axial scanning is typically much slower than lateral scanning in a conventional microscope.

There are currently several techniques for higher speed depth-resolved axial scanning. For table-top multiphoton microscopy, a second, identical objective focused onto a small mirror may be placed optically conjugate to the main objective and sample. The mirror may be translated axially at high speed due to its small size, resulting in an axial scan of the focus on the sample [8

8. E. J. Botcherby, R. Juskaitis, M. J. Booth, and T. Wilson, “Aberration-free optical refocusing in high numerical aperture microscopy,” Opt. Lett. 32(14), 2007–2009 (2007). [CrossRef] [PubMed]

]. Another method is to place a deformable mirror or spatial light modulator conjugate to the back focal plane of the imaging objective for arbitrary beam pointing and focusing [9

9. V. Nikolenko, B. O. Watson, R. Araya, A. Woodruff, D. S. Peterka, and R. Yuste, “SLM microscopy: scanless two-photon imaging and photostimulation using spatial light modulators,” Front Neural Circuits 2, 5 (2008). [CrossRef] [PubMed]

]. These techniques are effective, although expensive and complicated. More importantly, since electronics and mechanical moving parts are required near the sample, they cannot be readily miniaturized or incorporated into a flexible fiber probe. While high speed axial scanning is routinely achieved in optical coherence tomography (OCT) fiber probes [10

10. G. J. Tearney, M. E. Brezinski, B. E. Bouma, S. A. Boppart, C. Pitris, J. F. Southern, and J. G. Fujimoto, “In vivo endoscopic optical biopsy with optical coherence tomography,” Science 276(5321), 2037–2039 (1997). [CrossRef] [PubMed]

], OCT does not provide the chemical specificity and spectral information offered by confocal and multiphoton techniques.

2. Simultaneous spatial and temporal focusing

SSTF is a multiphoton technique in which a diffraction grating is imaged onto the sample, creating a wide-field, temporal focus (Fig. 1b
Fig. 1 Experimental setup for remote axial scanning. The group delay dispersion (GDD) of a femtosecond pulse is modulated by (a) a piezo-bimorph mirror in a folded 4-f grating pair setup. The GDD modulated pulse is coupled into a single-mode optical fiber. The output of the fiber undergoes (b) simultaneous spatial and temporal focusing (SSTF), in which a grating is imaged onto the sample forming a wide-field temporal focus. The sample emission is collected by the PMT detector assembly and correlated with the piezo-drive voltage.
) [11

11. G. Zhu, J. van Howe, M. Durst, W. Zipfel, and C. Xu, “Simultaneous spatial and temporal focusing of femtosecond pulses,” Opt. Express 13(6), 2153–2159 (2005). [CrossRef] [PubMed]

,12

12. D. Oron, E. Tal, and Y. Silberberg, “Scanningless depth-resolved microscopy,” Opt. Express 13(5), 1468–1476 (2005). [CrossRef] [PubMed]

]. The grating separates the spectral components of the pulse in space, causing the pulse width to vary as a function of axial position. For a transform-limited pulse, the minimum pulse width is recovered at the image plane of the system. Away from the image plane the pulse width broadens quickly. Because two-photon response is inversely proportional to the pulse width, an effective temporal focus is created at the image plane, providing axial confinement of the signal.

Axial scanning of the temporal focus by changing the GDD of the excitation pulse was experimentally shown and theoretically explained by Durst et al. [13

13. M. E. Durst, G. Zhu, and C. Xu, “Simultaneous spatial and temporal focusing for axial scanning,” Opt. Express 14(25), 12243–12254 (2006). [CrossRef] [PubMed]

]. The axial two-photon response of a SSTF system is given approximately by:

TPE(z)=C[1+(fz+βΩ2zRzR)2]1/2
(1)

with

zR=2f2k(s2+α2Ω2)
(2)

where C is a constant, f is the focal length of the objective lens, 2β is the GDD of the excitation, 2ln2Ω is the full width half maximum (FWHM) of a Gaussian excitation spectrum, k is the mean magnitude of the excitation wave vector, and s and αΩ are the monochromatic and full-spectrum spot sizes at the back aperture of the objective lens. The two-photon signal is axially confined, with a FWHM given by 23zR.

The position of the two-photon signal peak varies with the GDD. It can be shown from Eq. (1) that the displacement of the peak, Δz, is given by

Δz=βΩ2zR
(3)

By modulating the GDD of the excitation pulse, the temporal focus may be scanned over a range determined by the optical parameters of the system and the total available GDD.

3. Group delay dispersion modulation with a piezo bimorph mirror

To effectively use SSTF in an axial scanning setup, a method of modulating GDD over a large range at high speed is required. Typical methods for dispersion tuning include prism pairs and grating pairs [15

15. R. L. Fork, O. E. Martinez, and J. P. Gordon, “Negative dispersion using pairs of prisms,” Opt. Lett. 9(5), 150–152 (1984). [CrossRef] [PubMed]

,16

16. O. Martinez, “3000 times grating compressor with positive group-velocity dispersion – application to fiber compensation in 1.3–1.6 Mu-M region,” IEEE J. Quantum Electron. 23(1), 59–64 (1987). [CrossRef]

], but their tuning speed is limited by the mechanical translation of these bulky optical elements. Electronically adjustable devices, such as acousto-optic modulators (AOMs) [17

17. P. Tournois, “Acousto-optic programmable dispersive filter for adaptive compensation of group delay time dispersion in laser systems,” Opt. Commun. 140(4-6), 245–249 (1997). [CrossRef]

], spatial light modulators (SLMs) [18

18. A. M. Weiner, D. E. Leaird, J. S. Patel, and J. R. Wullert, “Programmable femtosecond pulse shaping by use of a multielement liquid-crystal phase modulator,” Opt. Lett. 15(6), 326–328 (1990). [CrossRef] [PubMed]

], and deformable mirrors [19

19. E. Zeek, K. Maginnis, S. Backus, U. Russek, M. Murnane, G. Mourou, H. Kapteyn, and G. Vdovin, “Pulse compression by use of deformable mirrors,” Opt. Lett. 24(7), 493–495 (1999). [CrossRef] [PubMed]

,20

20. C. Radzewicz, P. Wasylczyk, W. Wasilewski, and J. S. Krasiński, “Piezo-driven deformable mirror for femtosecond pulse shaping,” Opt. Lett. 29(2), 177–179 (2004). [CrossRef] [PubMed]

], can achieve programmable and high-speed dispersion tuning. These programmable devices can generate spectral phase of nearly arbitrary shape but at a high cost and with a limited GDD tuning range. In addition, their ability to generate higher-order dispersion is unnecessary, since tuning of the second-order group-delay dispersion is sufficient for remote axial scanning.

We demonstrate a GDD tuning device using a single piezo-bimorph mirror at the Fourier plane of a 4-f grating pair setup. Piezo bimorphs assume a quadratic shape with an applied voltage, allowing for large curvatures with high-speed electronic control [21

21. Q. Li, M. Lovell, J. Mei, and W. Clark, “A study of displacement distribution in a piezoelectric heterogeneous bimorph,” J. Mech. Des. 126(4), 757–762 (2004). [CrossRef]

,22

22. M. Steel, F. Harrison, and P. Harper, “The piezoelectric bimorph: An experimental and theoretical study of its quasistatic response,” J. Phys. D Appl. Phys. 11(6), 979–989 (1978). [CrossRef]

]. While pulse shaping using a piezo bimorph with multiple electrodes to independently address multiple sectors of the actuator has been demonstrated in the past [23

23. P. Wnuk, C. Radzewicz, and J. Krasiński, “Bimorph piezo deformable mirror for femtosecond pulse shaping,” Opt. Express 13(11), 4154–4159 (2005). [CrossRef] [PubMed]

], the use of a single piezo bimorph not only makes the device cost-effective but also provides large quadratic curvatures (i.e., GDD tuning range), avoiding both fabrication complexity and stroke limitations of multi-element deformable mirrors. Our device is low cost, robust (high damage threshold), high speed, and has a large GDD tuning range of more than 105 fs2 over a broad range of wavelengths.

The experimental setup of the GDD tuning device is shown in Fig. 1 (a). A ruled diffraction grating (1800 lines/mm) spectrally separates the beam from a mode-locked Ti:Sapphire laser (λ 0 = 775 nm, Δλ = 8 nm), which is then collimated by a spherical lens with a focal length of 30 cm. At the focal plane of the collimating lens, we place a piezo bimorph (T220-A4-503X, Piezo Systems, Inc.). The center of the piezo bimorph is fixed, allowing it to bend both forwards and backwards. A 380-micron thick pre-polished silicon wafer (University Wafer) is coated with gold to serve as a reflecting mirror, and it is mounted onto the piezo bimorph with double-sided Scotch tape as spacers. The piezo bimorph is driven by a function generator combined with a linear amplifier. The bending of the piezo bimorph can be described by [21

21. Q. Li, M. Lovell, J. Mei, and W. Clark, “A study of displacement distribution in a piezoelectric heterogeneous bimorph,” J. Mech. Des. 126(4), 757–762 (2004). [CrossRef]

,22

22. M. Steel, F. Harrison, and P. Harper, “The piezoelectric bimorph: An experimental and theoretical study of its quasistatic response,” J. Phys. D Appl. Phys. 11(6), 979–989 (1978). [CrossRef]

,24

24. “Introduction to piezo transducers” (Piezo Systems, Inc., 2007), http://www.piezo.com/tech2intropiezotrans.html, accessed June 24, 2009.

]:

y=3d312T2Vx2
(4)

where y is the axial displacement of the piezo, x is the lateral position of the piezo with respect to the optical axis, V is the applied voltage, d 31 is the piezoelectric coefficient, and T is the total thickness of the piezo. The difference in path length traveled by an individual monochromatic component is 2y due to the double pass configuration. The grating maps the individual frequency components, ω, to distinct lateral positions, such that for small spectral bandwidth, x = α D ω. The quadratic path length difference is then mapped to quadratic spectral phase, or GDD:

2ky=12GDD  ω2=12GDD(xαD)2
(5)

where k is the wavevector corresponding to the center wavelength λ 0. From Eqs. (4) and 5, the GDD at a driving voltage V is then:

GDD=12πλ0d31αD2T2V
(6)

Equation (6) shows that both normal and anomalous dispersions can be obtained in the same setup by changing the sign of the drive voltage. For example, for typical values V = 100 V, d 31 = 1.9x10−10 m/V, T = 0.51 mm, α D = 2.84x10−16 m/Hz, and λ 0 = 775 nm, the corresponding GDD will be 2.8x105 fs2.

To determine the GDD imposed on the pulse experimentally, we measure the pulse width of the beam exiting the folded grating pair using an interferometric second-order autocorrelator. The nonlinear element is a GaAsP photodiode. The beam is coupled out of the GDD device with a 50/50 beam splitter. A 100-fs pulse can be broadened to 4.2 ps by varying the drive voltage between +/− 100V (Fig. 2
Fig. 2 (a) Plot of measured GDD versus piezo-drive voltage. (b)-(d) Second-order interferometric autocorrelation traces of a 100 fs pulse at piezo drive voltages of (b) 100 V, (c) −10 V, (d) −100 V.
). Assuming a sech2 shape of the spectrum, the piezo-bimorph mirror produces a GDD of +/− 2.5x105 fs2, varying approximately linearly with voltage, and agreeing well with theory (Eq. (6). The device can be modulated at rates up to 100 Hz with no reduction in tuning range. The tuning range increases beyond 100 Hz as the piezo-bimorph mirror approaches its mechanical resonance (160 Hz), though we did not operate the device in this regime in order to prevent mechanical damage.

4. Axial scanning SSTF through a fiber

We use the GDD tuning device described above to perform remote axial scanning through a single mode fiber with SSTF. The experimental setup is shown in Fig. 1. The Ti:Sapphire laser is tuned to 755nm with spectral bandwidth of 8.5nm (full width half maximum). After the dispersion tuning device (Fig. 1a) the pulse is coupled into an air-core photonic bandgap fiber (Crystal Fibre, AIR-6-800), which has a nominal zero-dispersion wavelength of 754nm. The output of the fiber is collimated and incident on a 1200 lines per mm diffraction grating at 65 degrees such that the first-order diffraction angle of the center wavelength is normal to the plane of the grating. The diffracted beam is collimated by a spherical lens with a 40-cm focal length, and refocused onto the sample with an objective lens.

Emission from the sample is reflected by a dichroic mirror and detected by a photomultiplier tube (PMT). A function generator provides a sinusoidal signal used to modulate the piezo-bimorph mirror and to provide a trigger for photon counting of the PMT signal. The PMT signal is then correlated with the piezo-drive voltage, which is proportional to the change of GDD in the system and thereby the axial displacement of the temporal focus (Eqs. (3) and (6)). Because the temporal focus scans both forward and backward in one voltage cycle, the axial scan rate is twice the modulation rate of the GDD. The triggering setup allows multiple axial scans to be averaged in real time to improve the signal-to-noise ratio.

To demonstrate feasibility in a biological sample, we perform axial scans of excised mouse skin. The multiphoton spectral signal of mouse skin is well characterized by Palero and Gerritson et al. [25

25. J. A. Palero, H. S. de Bruijn, A. van der Ploeg van den Heuvel, H. J. Sterenborg, and H. C. Gerritsen, “Spectrally resolved multiphoton imaging of in vivo and excised mouse skin tissues,” Biophys. J. 93(3), 992–1007 (2007). [CrossRef] [PubMed]

]. The first fifteen to twenty microns of tissue comprise the epidermis, where multiphoton signal is dominated by intrinsic autofluorescence of cellular molecules, such as keratin and NADPH, in the 450 nm to 600 nm range. Beneath the epidermis is the dermis, which is primarily composed of structural proteins such as collagen and elastin fibers which give a strong second harmonic signal at one half the excitation wavelength (377.5 nm for excitation at 755 nm).

In this experiment we use a nominally 2.7-mm focal length water-immersion objective. The excitation wavelength is 755 nm and the pulse width is approximately 100 fs. The incident average power is 72 mW. We collect the signal with two separate PMT channels, one covering the 355 nm – 400 nm range targeting second harmonic generation, and the other covering the 500 nm – 650 nm range targeting autofluorescence. Remote axial scanning is performed by leaving the sample stationary and scanning the temporal focus by modulating the GDD. The thin film characterization data is used to generate a position axis from the piezo-drive voltage and to correct for variations in the two-photon response at different positions of the temporal focus. For comparison, we also acquire an axial scan of the tissue by mechanically stepping the sample through a stationary temporal focus with a translation stage.

The results are shown in Fig. 4
Fig. 4 Axial scans of mouse skin. Axial scan taken by moving the sample through the temporal focus with a translation stage is shown in (a). Axial scans by GDD modulation at 10 Hz and 200 Hz are shown in (b) and (c). The 500 nm to 650 nm channel shown is in red. The peak is produced by autofluorescence in the epidermis. The 355 nm to 400 nm channel is shown in blue. The signal is strongest in the deeper, fibrous tissue of the dermis, producing second harmonic generation.
. An axial scanning speed of 200 Hz is achieved (Fig. 4c), sufficient for overcoming motion artifacts for future in vivo imaging of live tissues. The epidermis and dermis are clearly seen in the autofluorescence and second harmonic channels respectively, separated by about 20 microns. The GDD scans faithfully reproduce the stage scan (Fig. 4a), demonstrating that remote axial scanning using GDD tuning in an SSTF setup is equivalent to a mechanical sample scan.

5. Discussion and conclusion

In this experiment, the axial scan speed was limited to 200 Hz by the mechanical resonance of the piezo bimorph, measured to be 160 Hz. The resonant frequency can be increased significantly by reducing the size of the piezo-bimorph mirror, allowing for faster scan speeds. The ultimate limitation on the scan speed is imposed by the brightness of the sample, i.e., the desired signal-to-noise ratio of the axial scan trace. As shown in our results, an adequate signal-to-noise ratio can be obtained with an axial scan rate between 10 and 200 Hz.

Because a wide-field focus is necessary for SSTF to achieve a large axial scan range, the two-photon response is significantly smaller for a given excitation pulse than that for a conventional point focus. The reduction in signal generation rate is partially made up for by the increased integration time. A typical point-scanning system has a pixel dwell time on the order of 10 µs or less, whereas a SSTF system with 10 axially resolved points scanned at 100 Hz has a pixel dwell time of 1 ms, one hundred times larger. Additionally, because the focal spot in SSTF is much larger than that of a point focus, more excitation power may be delivered to the sample without causing nonlinear photodamage. Therefore, the average excitation power may be increased to further improve the signal-to-noise ratio of the axial scan. We note that one-photon absorption in the near IR (e.g., 800 nm) is typically small in biological samples. For example, optical trappings over several seconds with approximately 100 mW average power are routinely used with minimal sample damage [26

26. S. P. Gross, “Application of optical traps in vivo,” Methods Enzymol. 361, 162–174 (2003). [CrossRef] [PubMed]

,27

27. K. C. Neuman and S. M. Block, “Optical trapping,” Rev. Sci. Instrum. 75(9), 2787–2809 (2004). [CrossRef] [PubMed]

]. In contrast, a tenth of a second or less is sufficient for one axial scan. In special circumstances where linear absorption is a concern, the signal-to-noise ratio can be improved by increasing the excitation pulse energy without increasing the average excitation power (i.e., by reducing the repetition rate).

The lateral width of the wide-field focus is dependent upon the spot size of the excitation beam on the diffraction grating and its demagnification onto the sample. A larger wide-field focus results in greater sample coverage and a longer available axial scan range, but results in decreased two-photon excitation. A smaller wide-field focus increases the two-photon excited signal over a narrower, more specific region of the sample, but reduces the available axial scan range before significant reduction in signal occurs. A more complete discussion of the impact of the lateral width can be found in Durst et al. [13

13. M. E. Durst, G. Zhu, and C. Xu, “Simultaneous spatial and temporal focusing for axial scanning,” Opt. Express 14(25), 12243–12254 (2006). [CrossRef] [PubMed]

]. In this experiment, the spot size on the diffraction grating was kept near 3 mm, resulting in wide-field foci of approximately 20 µm, 60 µm, and 140 µm on the sample for the objective lenses used. This choice is a trade-off between signal strength and the available axial scanning range.

We believe that the demonstrated remote axial scanning technique is best suited in a passive, flexible fiber probe for multiphoton excitation of axially resolved fluorescence and harmonic generation, bridging the gap between imaging optical endoscopes and non-imaging fiber optic probes. It has all the desirable attributes of a passive fiber probe but with added axial sectioning capability. As shown previously in depth-resolved tissue spectroscopy and imaging [1

1. Y. Wu, P. Xi, J. Qu, T. H. Cheung, and M. Y. Yu, “Depth-resolved fluorescence spectroscopy of normal and dysplastic cervical tissue,” Opt. Express 13(2), 382–388 (2005). [CrossRef] [PubMed]

3

3. W. R. Zipfel, R. M. Williams, R. Christie, A. Y. Nikitin, B. T. Hyman, and W. W. Webb, “Live tissue intrinsic emission microscopy using multiphoton-excited native fluorescence and second harmonic generation,” Proc. Natl. Acad. Sci. U.S.A. 100(12), 7075–7080 (2003). [CrossRef] [PubMed]

], the addition of axial sectioning to a conventional fiber probe will undoubtedly improve its diagnostic capability. The collection efficiency of such a probe can be enhanced through the use of large mode area or double-clad fibers [6

6. L. Fu, A. Jain, H. Xie, C. Cranfield, and M. Gu, “Nonlinear optical endoscopy based on a double-clad photonic crystal fiber and a MEMS mirror,” Opt. Express 14(3), 1027–1032 (2006). [CrossRef] [PubMed]

], allowing for high collection efficiency throughout the depth of focus as the focal plane is scanned. A dichroic mirror placed at an appropriate angle after the grating can redirect the two-photon signal into such a fiber without affecting the excitation beam.

In summary, we have demonstrated high speed, large range, chemically specific multiphoton axial scanning of excised mouse skin through a single-mode fiber using SSTF. Because scanning is achieved by modulating GDD on the proximal end of the fiber, this technique may be implemented in a passive multiphoton fiber probe capable of producing high speed axial scans in vivo with no moving parts or electronics at the distal end. Such a remote scanning multiphoton probe can be an excellent compliment to existing OCT probes. An integrated SSTF and OCT passive fiber probe can be used to obtain both one-photon reflectance and two-photon fluorescence and harmonic generation signal, potentially enhancing its diagnostic capability.

Acknowledgments

This work was made possible by National Institutes of Health (NIH) grant R21CA129648. The authors would like to thank Dr. Warren Zipfel for useful discussions and for generously lending equipment.

References and links

1.

Y. Wu, P. Xi, J. Qu, T. H. Cheung, and M. Y. Yu, “Depth-resolved fluorescence spectroscopy of normal and dysplastic cervical tissue,” Opt. Express 13(2), 382–388 (2005). [CrossRef] [PubMed]

2.

M. C. Skala, J. M. Squirrell, K. M. Vrotsos, J. C. Eickhoff, A. Gendron-Fitzpatrick, K. W. Eliceiri, and N. Ramanujam, “Multiphoton microscopy of endogenous fluorescence differentiates normal, precancerous, and cancerous squamous epithelial tissues,” Cancer Res. 65(4), 1180–1186 (2005). [CrossRef] [PubMed]

3.

W. R. Zipfel, R. M. Williams, R. Christie, A. Y. Nikitin, B. T. Hyman, and W. W. Webb, “Live tissue intrinsic emission microscopy using multiphoton-excited native fluorescence and second harmonic generation,” Proc. Natl. Acad. Sci. U.S.A. 100(12), 7075–7080 (2003). [CrossRef] [PubMed]

4.

R. Kiesslich, J. Burg, M. Vieth, J. Gnaendiger, M. Enders, P. Delaney, A. Polglase, W. McLaren, D. Janell, S. Thomas, B. Nafe, P. R. Galle, and M. F. Neurath, “Confocal laser endoscopy for diagnosing intraepithelial neoplasias and colorectal cancer in vivo,” Gastroenterology 127(3), 706–713 (2004). [CrossRef] [PubMed]

5.

B. A. Flusberg, J. C. Jung, E. D. Cocker, E. P. Anderson, and M. J. Schnitzer, “In vivo brain imaging using a portable 3.9 gram two-photon fluorescence microendoscope,” Opt. Lett. 30(17), 2272–2274 (2005). [CrossRef] [PubMed]

6.

L. Fu, A. Jain, H. Xie, C. Cranfield, and M. Gu, “Nonlinear optical endoscopy based on a double-clad photonic crystal fiber and a MEMS mirror,” Opt. Express 14(3), 1027–1032 (2006). [CrossRef] [PubMed]

7.

F. Helmchen, M. S. Fee, D. W. Tank, and W. Denk, “A miniature head-mounted two-photon microscope. high-resolution brain imaging in freely moving animals,” Neuron 31(6), 903–912 (2001). [CrossRef] [PubMed]

8.

E. J. Botcherby, R. Juskaitis, M. J. Booth, and T. Wilson, “Aberration-free optical refocusing in high numerical aperture microscopy,” Opt. Lett. 32(14), 2007–2009 (2007). [CrossRef] [PubMed]

9.

V. Nikolenko, B. O. Watson, R. Araya, A. Woodruff, D. S. Peterka, and R. Yuste, “SLM microscopy: scanless two-photon imaging and photostimulation using spatial light modulators,” Front Neural Circuits 2, 5 (2008). [CrossRef] [PubMed]

10.

G. J. Tearney, M. E. Brezinski, B. E. Bouma, S. A. Boppart, C. Pitris, J. F. Southern, and J. G. Fujimoto, “In vivo endoscopic optical biopsy with optical coherence tomography,” Science 276(5321), 2037–2039 (1997). [CrossRef] [PubMed]

11.

G. Zhu, J. van Howe, M. Durst, W. Zipfel, and C. Xu, “Simultaneous spatial and temporal focusing of femtosecond pulses,” Opt. Express 13(6), 2153–2159 (2005). [CrossRef] [PubMed]

12.

D. Oron, E. Tal, and Y. Silberberg, “Scanningless depth-resolved microscopy,” Opt. Express 13(5), 1468–1476 (2005). [CrossRef] [PubMed]

13.

M. E. Durst, G. Zhu, and C. Xu, “Simultaneous spatial and temporal focusing for axial scanning,” Opt. Express 14(25), 12243–12254 (2006). [CrossRef] [PubMed]

14.

R. Du, K. Bi, S. Zeng, D. Li, S. Xue, and Q. Luo, “Analysis of fast axial scanning scheme using temporal focusing with acousto-optic deflectors,” J. Mod. Opt. 56, 99–102 (2008).

15.

R. L. Fork, O. E. Martinez, and J. P. Gordon, “Negative dispersion using pairs of prisms,” Opt. Lett. 9(5), 150–152 (1984). [CrossRef] [PubMed]

16.

O. Martinez, “3000 times grating compressor with positive group-velocity dispersion – application to fiber compensation in 1.3–1.6 Mu-M region,” IEEE J. Quantum Electron. 23(1), 59–64 (1987). [CrossRef]

17.

P. Tournois, “Acousto-optic programmable dispersive filter for adaptive compensation of group delay time dispersion in laser systems,” Opt. Commun. 140(4-6), 245–249 (1997). [CrossRef]

18.

A. M. Weiner, D. E. Leaird, J. S. Patel, and J. R. Wullert, “Programmable femtosecond pulse shaping by use of a multielement liquid-crystal phase modulator,” Opt. Lett. 15(6), 326–328 (1990). [CrossRef] [PubMed]

19.

E. Zeek, K. Maginnis, S. Backus, U. Russek, M. Murnane, G. Mourou, H. Kapteyn, and G. Vdovin, “Pulse compression by use of deformable mirrors,” Opt. Lett. 24(7), 493–495 (1999). [CrossRef] [PubMed]

20.

C. Radzewicz, P. Wasylczyk, W. Wasilewski, and J. S. Krasiński, “Piezo-driven deformable mirror for femtosecond pulse shaping,” Opt. Lett. 29(2), 177–179 (2004). [CrossRef] [PubMed]

21.

Q. Li, M. Lovell, J. Mei, and W. Clark, “A study of displacement distribution in a piezoelectric heterogeneous bimorph,” J. Mech. Des. 126(4), 757–762 (2004). [CrossRef]

22.

M. Steel, F. Harrison, and P. Harper, “The piezoelectric bimorph: An experimental and theoretical study of its quasistatic response,” J. Phys. D Appl. Phys. 11(6), 979–989 (1978). [CrossRef]

23.

P. Wnuk, C. Radzewicz, and J. Krasiński, “Bimorph piezo deformable mirror for femtosecond pulse shaping,” Opt. Express 13(11), 4154–4159 (2005). [CrossRef] [PubMed]

24.

“Introduction to piezo transducers” (Piezo Systems, Inc., 2007), http://www.piezo.com/tech2intropiezotrans.html, accessed June 24, 2009.

25.

J. A. Palero, H. S. de Bruijn, A. van der Ploeg van den Heuvel, H. J. Sterenborg, and H. C. Gerritsen, “Spectrally resolved multiphoton imaging of in vivo and excised mouse skin tissues,” Biophys. J. 93(3), 992–1007 (2007). [CrossRef] [PubMed]

26.

S. P. Gross, “Application of optical traps in vivo,” Methods Enzymol. 361, 162–174 (2003). [CrossRef] [PubMed]

27.

K. C. Neuman and S. M. Block, “Optical trapping,” Rev. Sci. Instrum. 75(9), 2787–2809 (2004). [CrossRef] [PubMed]

OCIS Codes
(170.3880) Medical optics and biotechnology : Medical and biological imaging
(180.5810) Microscopy : Scanning microscopy
(230.2035) Optical devices : Dispersion compensation devices

ToC Category:
Microscopy

History
Original Manuscript: October 20, 2010
Revised Manuscript: November 7, 2010
Manuscript Accepted: December 2, 2010
Published: December 6, 2010

Citation
Adam Straub, Michael E. Durst, and Chris Xu, "High speed multiphoton axial scanning through an optical fiber in a remotely scanned temporal focusing setup," Biomed. Opt. Express 2, 80-88 (2011)
http://www.opticsinfobase.org/boe/abstract.cfm?URI=boe-2-1-80


Sort:  Author  |  Year  |  Journal  |  Reset  

References

  1. Y. Wu, P. Xi, J. Qu, T. H. Cheung, and M. Y. Yu, “Depth-resolved fluorescence spectroscopy of normal and dysplastic cervical tissue,” Opt. Express 13(2), 382–388 (2005). [CrossRef] [PubMed]
  2. M. C. Skala, J. M. Squirrell, K. M. Vrotsos, J. C. Eickhoff, A. Gendron-Fitzpatrick, K. W. Eliceiri, and N. Ramanujam, “Multiphoton microscopy of endogenous fluorescence differentiates normal, precancerous, and cancerous squamous epithelial tissues,” Cancer Res. 65(4), 1180–1186 (2005). [CrossRef] [PubMed]
  3. W. R. Zipfel, R. M. Williams, R. Christie, A. Y. Nikitin, B. T. Hyman, and W. W. Webb, “Live tissue intrinsic emission microscopy using multiphoton-excited native fluorescence and second harmonic generation,” Proc. Natl. Acad. Sci. U.S.A. 100(12), 7075–7080 (2003). [CrossRef] [PubMed]
  4. R. Kiesslich, J. Burg, M. Vieth, J. Gnaendiger, M. Enders, P. Delaney, A. Polglase, W. McLaren, D. Janell, S. Thomas, B. Nafe, P. R. Galle, and M. F. Neurath, “Confocal laser endoscopy for diagnosing intraepithelial neoplasias and colorectal cancer in vivo,” Gastroenterology 127(3), 706–713 (2004). [CrossRef] [PubMed]
  5. B. A. Flusberg, J. C. Jung, E. D. Cocker, E. P. Anderson, and M. J. Schnitzer, “In vivo brain imaging using a portable 3.9 gram two-photon fluorescence microendoscope,” Opt. Lett. 30(17), 2272–2274 (2005). [CrossRef] [PubMed]
  6. L. Fu, A. Jain, H. Xie, C. Cranfield, and M. Gu, “Nonlinear optical endoscopy based on a double-clad photonic crystal fiber and a MEMS mirror,” Opt. Express 14(3), 1027–1032 (2006). [CrossRef] [PubMed]
  7. F. Helmchen, M. S. Fee, D. W. Tank, and W. Denk, “A miniature head-mounted two-photon microscope. high-resolution brain imaging in freely moving animals,” Neuron 31(6), 903–912 (2001). [CrossRef] [PubMed]
  8. E. J. Botcherby, R. Juskaitis, M. J. Booth, and T. Wilson, “Aberration-free optical refocusing in high numerical aperture microscopy,” Opt. Lett. 32(14), 2007–2009 (2007). [CrossRef] [PubMed]
  9. V. Nikolenko, B. O. Watson, R. Araya, A. Woodruff, D. S. Peterka, and R. Yuste, “SLM microscopy: scanless two-photon imaging and photostimulation using spatial light modulators,” Front Neural Circuits 2, 5 (2008). [CrossRef] [PubMed]
  10. G. J. Tearney, M. E. Brezinski, B. E. Bouma, S. A. Boppart, C. Pitris, J. F. Southern, and J. G. Fujimoto, “In vivo endoscopic optical biopsy with optical coherence tomography,” Science 276(5321), 2037–2039 (1997). [CrossRef] [PubMed]
  11. G. Zhu, J. van Howe, M. Durst, W. Zipfel, and C. Xu, “Simultaneous spatial and temporal focusing of femtosecond pulses,” Opt. Express 13(6), 2153–2159 (2005). [CrossRef] [PubMed]
  12. D. Oron, E. Tal, and Y. Silberberg, “Scanningless depth-resolved microscopy,” Opt. Express 13(5), 1468–1476 (2005). [CrossRef] [PubMed]
  13. M. E. Durst, G. Zhu, and C. Xu, “Simultaneous spatial and temporal focusing for axial scanning,” Opt. Express 14(25), 12243–12254 (2006). [CrossRef] [PubMed]
  14. R. Du, K. Bi, S. Zeng, D. Li, S. Xue, and Q. Luo, “Analysis of fast axial scanning scheme using temporal focusing with acousto-optic deflectors,” J. Mod. Opt. 56, 99–102 (2008).
  15. R. L. Fork, O. E. Martinez, and J. P. Gordon, “Negative dispersion using pairs of prisms,” Opt. Lett. 9(5), 150–152 (1984). [CrossRef] [PubMed]
  16. O. Martinez, “3000 times grating compressor with positive group-velocity dispersion – application to fiber compensation in 1.3–1.6 Mu-M region,” IEEE J. Quantum Electron. 23(1), 59–64 (1987). [CrossRef]
  17. P. Tournois, “Acousto-optic programmable dispersive filter for adaptive compensation of group delay time dispersion in laser systems,” Opt. Commun. 140(4-6), 245–249 (1997). [CrossRef]
  18. A. M. Weiner, D. E. Leaird, J. S. Patel, and J. R. Wullert, “Programmable femtosecond pulse shaping by use of a multielement liquid-crystal phase modulator,” Opt. Lett. 15(6), 326–328 (1990). [CrossRef] [PubMed]
  19. E. Zeek, K. Maginnis, S. Backus, U. Russek, M. Murnane, G. Mourou, H. Kapteyn, and G. Vdovin, “Pulse compression by use of deformable mirrors,” Opt. Lett. 24(7), 493–495 (1999). [CrossRef] [PubMed]
  20. C. Radzewicz, P. Wasylczyk, W. Wasilewski, and J. S. Krasiński, “Piezo-driven deformable mirror for femtosecond pulse shaping,” Opt. Lett. 29(2), 177–179 (2004). [CrossRef] [PubMed]
  21. Q. Li, M. Lovell, J. Mei, and W. Clark, “A study of displacement distribution in a piezoelectric heterogeneous bimorph,” J. Mech. Des. 126(4), 757–762 (2004). [CrossRef]
  22. M. Steel, F. Harrison, and P. Harper, “The piezoelectric bimorph: An experimental and theoretical study of its quasistatic response,” J. Phys. D Appl. Phys. 11(6), 979–989 (1978). [CrossRef]
  23. P. Wnuk, C. Radzewicz, and J. Krasiński, “Bimorph piezo deformable mirror for femtosecond pulse shaping,” Opt. Express 13(11), 4154–4159 (2005). [CrossRef] [PubMed]
  24. “Introduction to piezo transducers” (Piezo Systems, Inc., 2007), http://www.piezo.com/tech2intropiezotrans.html , accessed June 24, 2009.
  25. J. A. Palero, H. S. de Bruijn, A. van der Ploeg van den Heuvel, H. J. Sterenborg, and H. C. Gerritsen, “Spectrally resolved multiphoton imaging of in vivo and excised mouse skin tissues,” Biophys. J. 93(3), 992–1007 (2007). [CrossRef] [PubMed]
  26. S. P. Gross, “Application of optical traps in vivo,” Methods Enzymol. 361, 162–174 (2003). [CrossRef] [PubMed]
  27. K. C. Neuman and S. M. Block, “Optical trapping,” Rev. Sci. Instrum. 75(9), 2787–2809 (2004). [CrossRef] [PubMed]

Cited By

Alert me when this paper is cited

OSA is able to provide readers links to articles that cite this paper by participating in CrossRef's Cited-By Linking service. CrossRef includes content from more than 3000 publishers and societies. In addition to listing OSA journal articles that cite this paper, citing articles from other participating publishers will also be listed.

Figures

Fig. 1 Fig. 2 Fig. 3
 
Fig. 4
 

« Previous Article  |  Next Article »

OSA is a member of CrossRef.

CrossCheck Deposited