1 September 2009 Extended in vivo anterior eye-segment imaging with full-range complex spectral domain optical coherence tomography
Author Affiliations +
J. of Biomedical Optics, 14(5), 050501 (2009). doi:10.1117/1.3213569
Abstract
We demonstrate the capability of full-range complex (FRC) spectral domain optical coherence tomography (SD-OCT) to image the anterior eye segment from the cornea to the posterior surface of the lens. With an adapted spectrometer design, we developed a SD-OCT system with an extended normal (single half-space) depth range of 7 mm (in air). This OCT-intrinsic depth range was doubled with a FRC technique. We demonstrate the performance of our OCT system by imaging the whole anterior segment of a healthy human eye in vivo.
Jungwirth, Baumann, Pircher, Götzinger, and Hitzenberger: Extended in vivo anterior eye-segment imaging with full-range complex spectral domain optical coherence tomography

Optical coherence tomography (OCT) is an imaging modality that enables high-resolution cross-sectional imaging of biological tissues and translucent materials.1, 2 Spectral domain (SD) OCT is a high-speed and high-sensitivity variant of OCT that largely replaced the older time domain variant in the recent years.

In SD-OCT, the depth-resolved information can be reconstructed by Fourier transform of the cross spectral density measured with a spectrometer located in the detection arm of an interferometer.3, 4 However, SD-OCT suffers from two drawbacks that restrict its measurement range.

First, the Fourier transform of the real-valued cross-spectral density is symmetrical about the zero path difference. Therefore, one cannot distinguish between positive and negative optical path differences with respect to the reference mirror. This effect particularly concerns imaging of objects with larger depth extensions, such as the anterior eye segment, where measurement ranges of the order of 10mm are needed. In order to suppress the mirror images, the so-called full-range complex (FRC) technique was introduced.5 In addition to the amplitude of the spectral interferogram, its phase is measured to reconstruct the full complex spectral interferogram—the analytic function. Inverse Fourier transformation of the analytic function directly yields the true object structures without any mirror terms. Several FRC approaches were developed that differ in the way of generating the π2 phase-shifted quadrature function of the spectral interferometric signal.6, 7, 8 An elegant method uses the phase modulation that is introduced by off-pivot-point illumination of the galvanometer scanner mirror.9, 10, 11 A second drawback of SD-OCT is the spectrometer-intrinsic depth range, which is limited by its spectral resolution. Until now, the depth range of standard SD-OCT systems is 3mm , which can be doubled by applying FRC methods. However, this axial measurement range is not sufficient to cover the entire anterior eye segment.

In this letter, we demonstrate an SD-OCT system with a modified spectrometer design combined with a FRC measurement range doubling that achieves an imaging depth of 14mm , sufficient to cover the human anterior eye segment from the cornea to the posterior surface of the lens.

Figure 1 shows a schematic diagram of our system. A superluminescent diode (Superlum, Moscow) with a center wavelength of 835nm and a bandwidth (FWHM) of 18nm was used as the light source. The round trip coherence length was 17μm . The collimated beam ( 1.5mm diam) was divided by a 5050 nonpolarizing beamsplitter into a reference and a sample beam. A variable neutral density filter was mounted in the reference arm to adjust the light power so that the line-scan camera of the spectrometer is operated close to the saturation limit to get maximum sensitivity. In the sample arm, a galvanometer scanner was mounted on an x-y translation stage for correct adjusting of the scanner position to achieve a π2 phase shift between adjacent A scans.9 The scanner was driven by a saw-tooth voltage generated by a DAQ-card (National Instruments, PCI 6110, Austin, TX). An achromatic object lens with a focal length of 80mm was used to focus the beam onto the sample. This provided a transversal resolution of 57μm with a confocal range of 6mm . Sample and reference beams were recombined at the 5050 splitter, coupled into a single mode fiber and guided to the spectrometer where the real part of the spectral interferogram S(x,λ) was recorded.

Fig. 1

Schematic setup of the FRC-SD-OCT system. SLD, super luminescent diode; C, collimator; NPBS, nonpolarizing beamsplitter; VDF, variable density filter; M, reference mirror; GS, x-y galvanometer scanner; OL, object lens; S, sample; DAQ, data acquisition card; SMF, single-mode fiber; DG, diffraction grating; CL, camera lens; LSC, line scan camera; and FGC, frame grabber card.

050501_1_003905jbo1.jpg

The spectrometer consisted of a transmission diffraction grating (Wasatch Photonics, Logan, Utah) with 1500linesmm , an achromatic camera lens with a focal length of 300mm , and a 2048pixel line-scan camera (Atmel, Aviiva M2 CL 2014, San Jose, CA) with 14×14μm2pixel size. In our configuration, the spectrometer resolution was 25pm . The SD-OCT intrinsic depth range, which is limited by the Nyquist sampling theorem, was measured with 7mm (in air).6 After applying the full-range algorithm, the depth range was doubled to an axial imaging range of 14mm . The probing beam power on the cornea was 2mW , which is well below the safety limits.12 The integration time per A scan was set to 50μs to optimize the trade-off between mirror term suppression and sensitivity. With this setting, the sensitivity of the system was measured with 106dB near zero position. The sensitivity decrease was 17dB over three-quarters of the depth range. The system worked with an A-scan rate of 20kHz . A single B scan with 2048 A-scans was recorded in 100ms . The acquisition time for a 3-D scan with 120 B scans was 15s . The scanning range covered the whole transversal width of the anterior eye segment ( 14mm for a single B scan and 14×14mm2 for a 3-D scan).

In conventional SD-OCT, the intensity distribution I(x,z) (which represents the depth profiles) is retrieved by inverse Fourier transform of the recorded spectral interferogram I(x,z)=FTkz1{S(x,k)} , where x is the transversal scanning direction, z the axial depth range, and k the wavenumber. Prior to the Fourier transform, fixed pattern noise and dc term were removed by subtracting a mean spectrum (averaged over 2048 A scans) from each spectral data set, followed by rescaling the spectral data from λ space into k space.

As mentioned above, the Fourier transform of a real valued function is Hermitian, and therefore, the depth profile is symmetrical about zero path difference, giving rise to mirror artifacts in conventional SD-OCT. To suppress these mirror artifacts and double the measurement range, we used a phase shift introduced by the x scanning mirror.9, 10, 11 In brief, the sample beam hits the fast scanning mirror slightly away from the scanner pivot axis. Therefore, during the transversal scan, the optical path length is changed. A constant phase shift between adjacent A scans is generated that depends on the mirror axis offset. If the phase difference is set appropriately (π2) , one can reconstruct the complex spectral interferogram by Hilbert transform of S(x,k) along the transverse coordinate x for each wavenumber k . Finally, an inverse Fourier transform of each complex spectral A scan yields the depth profiles with suppressed mirror images.

The measured spectral interferograms were transferred via camera link and a high-speed frame grabber card (National Instruments, PCI 1428, Austin, Taxas) to a personal computer, where the data were stored and postprocessed.

We demonstrate the performance of our system by 2-D and 3-D imaging of the human anterior eye segment in vivo. Figure 2 shows a B scan. The signal intensity was plotted on a logarithmic gray scale and covers an image size of 14 (x)×14 ( z , optical distance) mm2 . Figure 2a shows a SD-OCT image obtained by inverse fast Fourier transform (FFT) of the spectral interferogram without applying FRC reconstruction. The object structure is disturbed by overlapping of mirror images. Figure 2b shows the same data set with FRC postprocessing. Note that the imaging depth ranges from the front surface of the cornea to the posterior surface of the lens. Even the epithelium of the cornea and backscattered intensity within the lens can be observed, as well as the lens capsule. However, there are still some residual mirror artifacts from highly backscattering structures, such as the iris.

Fig. 2

In vivo measurements of human anterior eye segment: (a) B scan with 2048 A scans obtained by standard SD-OCT processing; (b) full-range reconstruction by FFT of the complex spectral interferometric signal; image range from cornea to back surface of the lens. Extinction ratio at the iris: 22dB ; image size: 14×14mm2 ; and Dynamic range 50dB .

050501_1_003905jbo2.jpg

To quantify the mirror term suppression of our system, the extinction ratio was measured within a highly backscattering structure (iris in vivo) and at a weakly scattering black synthetic (nonmoving) surface.9 Only pixels with an intensity level above a certain threshold (noise level) in both imaging regions (corresponding to the positive and negative frequencies) were used to calculate the extinction ratio. With this convention, the extinction ratio was measured from Fig. 2b with 22dB in contrast to the nonmoving sample with 36dB . The reduced extinction ratio might be caused by sample motion that leads to phase instabilities and loss in mirror term suppression efficiency. Axial sample motion of > 2mms would inverse the suppression effect (suppressing the real image and enhancing the mirror image).9

Figure 3 shows the anterior eye segment during the accommodation from the far point (a) to the near point (b). The bright lines in both figures indicate the lens surfaces and demonstrate the thickness-change of the lens. Videos 1 shows a 3-D scan of the anterior eye segment. It contains 120 sequenced B scans, which were recorded during one sweep of the y scanner mirror. The size of the 3-D scan is approximately 14(x)×14(y)×14(z)mm3 . Videos 2 shows the same 3-D data set in the en face plane.

Fig. 3

OCT B-scans during the accommodation of the eye from (a) the far point to (b) the near point. Changes of the anterior eye segment, especially the thickness of the lens, are visible. The white lines are for better visualization of the lens surface position changes during accommodation.

050501_1_003905jbo3.jpg

Video 1

3-D scan of the anterior eye segment; movie contains sequence of 120 B scans that were recorded in 15s . Size: 14×14×14mm3 (QuickTime, 4.5MB ). .

050501_1_003905jbov1.jpg
10.1117/1.3213569.1

Video 2

Video derived by the same data set showing the en face cross sections of the anterior eye segment from the cornea via the iris to the lens. Size: 14×14×14mm3 (QuickTime, 2.6MB ). .

050501_1_003905jbov2.jpg
10.1117/1.3213569.2

One drawback of this method is that only a fixed scanning pattern (transversal range and speed) can be used for a specific scanning-mirror pivot-point offset. To overcome this problem, a motorized mount for the transverse scanner can be used. However, this would result in a more expensive and more complex system.

Conclusion

In conclusion, we have developed a SD-OCT system with an extended depth range. With the high sensitivity and high speed of the instrument, the whole anterior eye segment from the cornea to the posterior surface of the lens could be imaged in vivo with a recording time of 100ms per B scan at an A scan rate of 20kHz ; 120 sequenced B scans formed a 3-D scan, which was recorded in 15s . Possible clinical applications of our system may be in cataract and glaucoma (chamber angle) diagnostics, as well as in accommodation studies.

Acknowledgments

Technical support by C. Wölfl and financial support by the Austrian Science Fund (FWF Grant No. P 19624-B02) are gratefully acknowledged.

References

1. 

D. Huang, E. A. Swanson, C. P. Lin, J. S. Schumann, W. G. Stinson, W. Chang, M. Hee, T. Flotte, K. Gregory, C. A. Puliafito, and J. G. Fujimoto, “Optical coherence tomography,” Science0036-8075 254, 1178–1181 (1991).10.1126/science.1957169Google Scholar

2. 

A. F. Fercher, W. Drexler, C. K. Hitzenberger, and T. Lasser, “Optical coherence tomography-principles and applications,” Rep. Prog. Phys.0034-4885 66, 239–303 (2003).10.1088/0034-4885/66/2/204Google Scholar

3. 

A. F. Fercher, C. K. Hitzenberger, G. Kamp, and S. Y. El-Zaiat, “Measurement of intraocular distancs by backscattering spectral interferometry,” Opt. Commun.0030-4018 117, 43–48 (1995).10.1016/0030-4018(95)00119-SGoogle Scholar

4. 

G. Häusler and M. W. Lindner, “Coherence radar and spectral radar—new tools for dermatological diagnosis,” J. Biomed. Opt.1083-3668 3, 21–31 (1998).10.1117/1.429899Google Scholar

5. 

A. F. Fercher, R. Leitgeb, C. K. Hitzenberger, H. Sattmann, and M. Wojtkowski, “Complex spectral interferometry OCT,” Proc. SPIE0277-786X 3564, 173–178 (1999).10.1117/12.339152Google Scholar

6. 

M. Wojtkowski, A. Kowalczyk, R. Leitgeb, and A. Fercher, “Full range complex spectral optical coherence tomography technique in eye imaging,” Opt. Lett.0146-9592 27, 1415–1417 (2002).10.1364/OL.27.001415Google Scholar

7. 

R. Leitgeb, C. K. Hitzenberger, A. Fercher, and T. Bajraszewski, “Phase-shifting algorithm to achieve high-speed long-depth-range probing by frequency-domain optical coherence tomography,” Opt. Lett.0146-9592 28, 2291–2203 (2003).10.1364/OL.28.002201Google Scholar

8. 

E. Götzinger, M. Pircher, R. Leitgeb, and C. K. Hitzenberger, “High speed full range complex spectral domain optical coherence tomography,” Opt. Express1094-4087 13, 583–594 (2005).10.1364/OPEX.13.000583Google Scholar

9. 

B. Baumann, M. Pircher, E. Götzinger, and C. K. Hitzenberger, “Full range complex spectral domain optical coherence tomography without additional phase shifters,” Opt. Express1094-4087 15, 13375–13387 (2007).10.1364/OE.15.013375Google Scholar

10. 

L. An and R. Wang, “Use of a scanner to modulate spatial interferograms for in vivo full-range Fourier-domain optical coherence tomography,” Opt. Lett.0146-9592 32, 3423–3425 (2007).10.1364/OL.32.003423Google Scholar

11. 

R. Leitgeb, R. Michaely, T. Lasser, and S. Sekhar, “Complex ambiguity-free Fourier domain optical coherence tomography through transverse scanning,” Opt. Lett.0146-9592 32, 3453–3455 (2007).10.1364/OL.32.003453Google Scholar

12. 

International Electrotechnical Commission, Safety of laser products—Part 1: Equipment classification and requirements, IEC 60825–1 Ed. 2 (2001).Google Scholar

Johannes Jungwirth, Bernhard Baumann, Michael Pircher, Erich Götzinger, Christoph K. Hitzenberger, "Extended in vivo anterior eye-segment imaging with full-range complex spectral domain optical coherence tomography," Journal of Biomedical Optics 14(5), 050501 (1 September 2009). http://dx.doi.org/10.1117/1.3213569
JOURNAL ARTICLE
3 PAGES


SHARE
KEYWORDS
Mirrors

Eye

Image segmentation

Optical coherence tomography

In vivo imaging

Imaging systems

Cornea

Back to Top