Abstract
Over the last 50 years the introduction of several imaging technologies have been pivotal in reducing mortality associated with coronary artery disease. However coronary disease continues to be the leading cause of mortality in the industrialized world. Optical coherence tomography (OCT) has recently been introduced for micron scale intravascular imaging. It is analogous to ultrasound, measuring the intensity of back-reflected infrared light instead of sound. Some of the advantages of OCT include its resolution, which is higher than any currently available imaging technology and acquisition rates are near video speed. Unlike ultrasound, OCT catheters consist of simple fiber optics and contain no transducers within their frame, thereby making imaging catheters both inexpensive and small. Currently, the smallest catheters have a cross-sectional diameter of 0.014”. OCT systems are compact and portable and can be combined with a range of spectroscopic techniques. We review the application of OCT to intracoronary imaging.
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Acknowledgements
Our cardiovascular OCT work was achieved by James Fujimoto, Xingde Li, Neil Weissman, Herman Gold, Gary Tearney, Brett Bouma, Costas Pitris, Stephen Boppart, Kathleen Saunders, Christine Jesser, and James Southern. Most of the research was sponsored in part by the National Institutes of Health, the Medical Free Electron Laser Program, Office of Naval Research Contract, and the Whitaker Foundation.
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Appendix
Appendix
Low Coherence Interferometry and Resolution
The heart of the OCT system is a Michelson interferometer [18,41]. If the illuminating source generates light with a broad bandwidth, then the autocorrelation function or AC-coupled photon current representing the interference is then proportional to:
where I(δl) is the intensity at the detector, rsrr is the product of the reflections off the sample and mirror, Re[F{S(ω)}] is the real component of the Fourier transform of the power spectrum of the source, ω0 is the center frequency of the source, and τp is the phase delay. The width of the spectrum and the width of the autocorrelation function (coherence length) are inversely related via the Fourier transform. Therefore, the resolution increases (shorter coherence length) with increasing source bandwidth [42].
If the source has a Gaussian spectrum with a FWHM (full width half maximum) bandwidth, δλ, and a center λ0, then the coherence length (δl) or axial resolution is
The lateral resolution is determined essentially by the focusing power of the system or the lens chosen. It is described by the formula:
where d is the spot size or FWHM of the Gaussian spatial distribution, and b is the confocal parameter, which is twice the Rayleigh parameter.
System Dynamic Range
OCT has been designed near the shot noise limit by choosing a Doppler frequency (frequency shift from moving mirror) above 10 KHz to avoid 1/f noise and a proper transimpedance amplifier resistance and reference arm voltage to overcome thermal noise [42,43]. For quantum noise detection, the theoretical maximum SNR that can be achieved with OCT under the assumption of infinite linearity of electronics, no squeezing, and infinite dynamic range of the digitization electronics can be expressed:
where ηPs/2hv is the number of electrons per unit time generated by the detector due to returning light and 1/NEB band pass filter bandwidth. The measured signal-to-noise ratio for the system ranges from 100–120 dB and was determined from the maximum signal measured off a mirror divided by the noise.
Grating Based Delay Line
It was stated that acquisition rate is determined primarily by how quickly the pathlength can be changed in the reference arm [20]. One of the most significant advances was the grating-based delay line that was developed for high speed OCT imaging. The delay line works as follows. Light from the reference arm is directed at a grating. The grating disperses the beam, resulting in a Fourier transform. The dispersed light is focused on a tilted mirror and reflects off the mirror, and is focused back on the grating where it undergoes an inverse Fourier transform. The tilt in the mirror results in a linear phase ramp. A linear phase ramp in the frequency domain results in a group delay in the time domain. By changing the angle of the mirror, different group delays are introduced that determine the acquisition rate. The groups and phase delays are controlled separately in this embodiment. The group delay is controlled by the angle of the mirror while the phase delay is controlled by the position of the center of the bandwidth on the mirror. An additional advantage is that dispersion can be controlled without a prism by altering the position of the lens relative to the grating.
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Patel, N., Stamper, D. & Brezinski, M. Review of the Ability of Optical Coherence Tomography to Characterize Plaque, Including a Comparison with Intravascular Ultrasound. Cardiovasc Intervent Radiol 28, 1–9 (2005). https://doi.org/10.1007/s00270-003-0021-1
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DOI: https://doi.org/10.1007/s00270-003-0021-1