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Ultrahigh resolution Fourier domain optical coherence tomography

R. A. Leitgeb, W. Drexler, A. Unterhuber, B. Hermann, T. Bajraszewski, T. Le, A. Stingl, and A. F. Fercher

Open Access Open Access

Abstract

We present, for the first time, in vivo ultrahigh resolution (~2.5 μm in tissue), high speed (10000 A-scans/second equivalent acquisition rate sustained over 160 A-scans) retinal imaging obtained with Fourier domain (FD) OCT employing a commercially available, compact (500×260mm), broad bandwidth (120 nm at full-width-at-half-maximum centered at 800 nm) Titanium:sapphire laser (Femtosource Integral OCT, Femtolasers Produktions GmbH). Resolution and sampling requirements, dispersion compensation as well as dynamic range for ultrahigh resolution FD OCT are carefully analyzed. In vivo OCT sensitivity performance achieved by ultrahigh resolution FD OCT was similar to that of ultrahigh resolution time domain OCT, although employing only 2–3 times less optical power (~300 μW). Visualization of intra-retinal layers, especially the inner and outer segment of the photoreceptor layer, obtained by FDOCT was comparable to that, accomplished by ultrahigh resolution time domain OCT, despite an at least 40 times higher data acquisition speed of FD OCT.

©2004 Optical Society of America

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Figures (6)
Fig. 1.
Fig. 1. Schematic of the ultrahigh resolution FD OCT system: Ti:Sapp, broad bandwidth Titanium:sapphire laser (Femtosource Integral OCT); Ch, Chopper wheel; DF, neutral density filter; DC, dispersion control; DG, diffraction grating; X-Y-Sc, transverse galvo scanners; S, sample; SYNC, microelectronics for synchronizing system components; PC, personal computer; CCD, charge coupled device.

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Fig. 2.
Fig. 2. (a) recorded spectrum (black line) with dispersion and associated signal phase (red line). (b) Time domain signal after FFT without (black line) and with resampling (red line) of the recorded spectrum. The blue line shows the coherence envelope after the coordinate change λ→K.

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Fig. 3.
Fig. 3. (a) dependence of Ns,max and Nref to the load factor γ. (b) Dynamic range in the shot noise limit without (ξ=0) and with (ξ=0.2) incoherent background (N sat = 300 k e-, N=1024).

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Fig. 4.
Fig. 4. Relation of shot noise to RIN. (Nsat = 400 ke-, λ cent=820nm, FWHM=100nm, N=1024).

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Fig. 5.
Fig. 5. Effect of spectral zero padding to increase sampling point density in the time domain. The values shown on the x-axes are optical path lengths.

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Fig. 6.
Fig. 6. (a) Ultrahigh resolution by Fourier Domain optical coherence tomography with 10 kHz A-scan rate, 300μW at the sample, and 3μm axial resolution in free space across the foveal region of the retina. (b) Comparison to time domain optical coherence tomography with 130 Hz A-scan rate, 800μW at the sample, and ~3μm axial resolution in the retina. (c) Enlarged section of (a). (d) Enlarged section of (b).The imaged eyes are of different healthy volunteers. The white scale bars represent 100μm. The tomograms in (a) and (b) spread over ~5mm laterally, the sections in (c) and (d) over ~1,5mm. No image processing was applied. (NFL, nerve fiber layer; GCL, ganglion cell layer; IPL/OPL, inner/outer plexiform layer; INL, inner nuclear layer; ELM, external limiting membrane; ISPR/OSPR, inner/outer segment photo receptor layer; RPE, retinal pigment epithelium.)

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Equations (2)

Equations on this page are rendered with MathJax. Learn more.

I ( λ ) = I r ( λ ) + I s ( λ ) + 2 I r ( λ ) I s ( λ ) cos ( 2 f ( λ ) Δz + g ( λ ) ) ,
DR = N sample max N ref N sample min N ref = N sat γ ( 1 + γ − 2 γ ) 2 / N .
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