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Light is split into and recombined from reference and sample arm, respectively. In time domain OCT the pathlength of the reference arm is varied in time the reference mirror is translated longitudinally.
A property of low coherence interferometry is that interference, i. This interference is called auto correlation in a symmetric interferometer both arms have the same reflectivity , or cross-correlation in the common case.
The envelope of this modulation changes as pathlength difference is varied, where the peak of the envelope corresponds to pathlength matching.
Due to the coherence gating effect of OCT the complex degree of coherence is represented as a Gaussian function expressed as .
In equation 2 , the Gaussian envelope is amplitude modulated by an optical carrier. The peak of this envelope represents the location of the microstructure of the sample under test, with an amplitude dependent on the reflectivity of the surface.
The optical carrier is due to the Doppler effect resulting from scanning one arm of the interferometer, and the frequency of this modulation is controlled by the speed of scanning.
Therefore, translating one arm of the interferometer has two functions; depth scanning and a Doppler-shifted optical carrier are accomplished by pathlength variation.
In OCT, the Doppler-shifted optical carrier has a frequency expressed as. The axial and lateral resolutions of OCT are decoupled from one another; the former being an equivalent to the coherence length of the light source and the latter being a function of the optics.
The axial resolution of OCT is defined as. In frequency domain OCT FD-OCT the broadband interference is acquired with spectrally separated detectors either by encoding the optical frequency in time with a spectrally scanning source or with a dispersive detector, like a grating and a linear detector array.
Due to the Fourier relation Wiener-Khintchine theorem between the auto correlation and the spectral power density the depth scan can be immediately calculated by a Fourier-transform from the acquired spectra, without movement of the reference arm.
The parallel detection at multiple wavelength ranges limits the scanning range, while the full spectral bandwidth sets the axial resolution.
Thereby the information of the full depth scan can be acquired within a single exposure. The drawbacks of this technology are found in a strong fall-off of the SNR, which is proportional to the distance from the zero delay and a sinc-type reduction of the depth dependent sensitivity because of limited detection linewidth.
One pixel detects a quasi-rectangular portion of an optical frequency range instead of a single frequency, the Fourier-transform leads to the sinc z behavior.
Additionally the dispersive elements in the spectroscopic detector usually do not distribute the light equally spaced in frequency on the detector, but mostly have an inverse dependence.
Therefore, the signal has to be resampled before processing, which can not take care of the difference in local pixelwise bandwidth, which results in further reduction of the signal quality.
However, the fall-off is not a serious problem with the development of new generation CCD or photodiode array with a larger number of pixels.
Synthetic array heterodyne detection offers another approach to this problem without the need for high dispersion. Here the spectral components are not encoded by spatial separation, but they are encoded in time.
The spectrum is either filtered or generated in single successive frequency steps and reconstructed before Fourier-transformation. By accommodation of a frequency scanning light source i.
Drawbacks are the nonlinearities in the wavelength especially at high scanning frequencies , the broadening of the linewidth at high frequencies and a high sensitivity to movements of the scanning geometry or the sample below the range of nanometers within successive frequency steps.
More precisely, interferometric images are created by a Michelson interferometer where the path length difference is varied by a fast electric component usually a piezo mirror in the reference arm.
These images acquired by a CCD camera are combined in post-treatment or on-line by the phase shift interferometry method, where usually 2 or 4 images per modulation period are acquired, depending on the algorithm used.
The "en-face" tomographic images are thus produced by a wide-field illumination, ensured by the Linnik configuration of the Michelson interferometer where a microscope objective is used in both arms.
Furthermore, while the temporal coherence of the source must remain low as in classical OCT i. Focusing the light beam to a point on the surface of the sample under test, and recombining the reflected light with the reference will yield an interferogram with sample information corresponding to a single A-scan Z axis only.
Scanning of the sample can be accomplished by either scanning the light on the sample, or by moving the sample under test.
A linear scan will yield a two-dimensional data set corresponding to a cross-sectional image X-Z axes scan , whereas an area scan achieves a three-dimensional data set corresponding to a volumetric image X-Y-Z axes scan.
Systems based on single point, confocal, or flying-spot time domain OCT, must scan the sample in two lateral dimensions and reconstruct a three-dimensional image using depth information obtained by coherence-gating through an axially scanning reference arm Fig.
Two-dimensional lateral scanning has been electromechanically implemented by moving the sample  using a translation stage, and using a novel micro-electro-mechanical system scanner.
Parallel or full field OCT using a charge-coupled device CCD camera has been used in which the sample is full-field illuminated and en face imaged with the CCD, hence eliminating the electromechanical lateral scan.
By stepping the reference mirror and recording successive en face images a three-dimensional representation can be reconstructed. Three-dimensional OCT using a CCD camera was demonstrated in a phase-stepped technique,  using geometric phase shifting with a Linnik interferometer ,  utilising a pair of CCDs and heterodyne detection,  and in a Linnik interferometer with an oscillating reference mirror and axial translation stage.
Optical coherence tomography is an established medical imaging technique and is used across several medical specialties including ophthalmology and cardiology, and is widely used in basic science research applications.
Ocular or ophthalmic OCT is used heavily by ophthalmologists and Optometrists to obtain high-resolution images of the retina and anterior segment.
More recently, ophthalmic OCT devices have been engineered to perform similar functions as fluorescein angiography , but without the need for injectable dye.
This new OCT angiography OCTA  technique is still in development, but has shown promise for assessing retinal microvasculature pathology. OCTA has the potential for evaluating the effects of intensified antithrombotic therapy.
Future research and development will extend the use of OCTA beyond the realm of ophthalmology. In the setting of cardiology, OCT is used to image coronary arteries in order to visualize vessel wall lumen morphology and microstructure at a resolution 10 times higher than other existing modalities such as intravascular ultrasounds and x-ray angiography Intracoronary Optical Coherence Tomography.
Guillermo James Tearney and Prof. Brett Bouma based at Massachusetts General Hospital in The higher imaging speed of FD-OCT enabled the widespread adoption of this imaging technology for coronary artery imaging.
Recent developments of intravascular OCT included the combination with other optical imaging modalities. Researchers have used OCT to produce detailed images of mice brains, through a "window" made of zirconia that has been modified to be transparent and implanted in the skull.
OCT systems with feedback can be used to control manufacturing processes. With high speed data acquisition,  and sub-micron resolution, OCT is adaptable to perform both inline and off-line.
From Wikipedia, the free encyclopedia. Angle-resolved low-coherence interferometry Ballistic photon Confocal microscopy Interferometry Intracoronary Optical Coherence Tomography Leica Microsystems Medical imaging Novacam Technologies Optical heterodyne detection Optical projection tomography Terahertz tomography Tomography.
Retrieved 28 May Optical Instrumentation for Biomedical Laser Applications. In von Bally, G. Backscattering Optical Heterodyne Tomography.
Journal of Biomedical Optics. American Journal of Ophthalmology. A report by the American Academy of Ophthalmology".
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Care must be taken to exclude noninfectious causes of symptoms. Norovirus gastroenteritis both criteria 1 and 2 must be present.
At least 1 of the following GI subcriteria Diarrhea: Clostridium difficile infection both criteria 1 and 2 must be present.
Individuals previously infected with C. In the setting of an outbreak of GI infection, individuals could have positive test results for presence of C.
It is important that other surveillance criteria be used to differentiate infections in this situation.
One of the following GI subcriteria Diarrhea: