Optical coherence tomography

Summary

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Optical coherence tomography (OCT) is an imaging technique that uses interferometry with short-coherence-length light to obtain micrometer-level depth resolution and uses transverse scanning of the light beam to form two- and three-dimensional images from light reflected from within biological tissue or other scattering media. Short-coherence-length light can be obtained using a superluminescent diode (SLD) with a broad spectral bandwidth or a broadly tunable laser with narrow linewidth. The first demonstration of OCT imaging (in vitro) was published by a team from MIT and Harvard Medical School in a 1991 article in the journal Science.[1] The article introduced the term "OCT" to credit its derivation from optical coherence-domain reflectometry, in which the axial resolution is based on temporal coherence.[2] The first demonstrations of in vivo OCT imaging quickly followed.[3][4][5]

A high-resolution spectral-domain OCT scan (3×3 mm) of a dry age-related macular degeneration eye showing geographic atrophy and drusen in macula on both cross-sectional and en face fly-through.

The first US patents on OCT by the MIT/Harvard group described both a time-domain OCT (TD-OCT) system[6][7] and a Fourier-domain OCT (FD-OCT) system of the swept-source variety.[6] These patents were licensed by Zeiss and formed the basis of the first generations of OCT products until 2006. Tanno et al. obtained a patent on optical heterodyne tomography (similar to TD-OCT) in Japan in the same year.[8]

In the decade preceding the invention of OCT, interferometry with short-coherence-length light had been investigated for a variety of applications.[9][10][11][12][13][14][15][16][17][18][19][20]  The potential to use interferometry for imaging was proposed,[20] and measurement of retinal elevation profile and thickness had been demonstrated.[19]

The initial commercial clinical OCT systems were based on point-scanning TD-OCT technology, which primarily produced cross-sectional images due to the speed limitation (tens to thousands of axial scans per second). Fourier-domain OCT became available clinically 2006, enabling much greater image acquisition rate (tens of thousands to hundreds of thousands axial scans per second) without sacrificing signal strength. The higher speed allowed for three-dimensional imaging, which can be visualized in both en face and cross-sectional views. Novel contrasts such as angiography, elastography, and optoretinography also became possible by detecting signal change over time. Over the past three decades, the speed of commercial clinical OCT systems has increased more than 1000-fold, doubling every three years and rivaling Moore's law of computer chip performance. Development of parallel image acquisition approaches such as line-field and full-field technology may allow the performance improvement trend to continue.

OCT is most widely used in ophthalmology, in which it has transformed the diagnosis and monitoring of retinal diseases, optic nerve diseases, and corneal diseases. It has greatly improved the management of the top three causes of blindness – macular degeneration, diabetic retinopathy, and glaucoma – thereby preventing vision loss in many patients. By 2016 OCT was estimated to be used in more than 30 million imaging procedures per year worldwide.[21]

OCT angioscopy is used in the intravascular evaluation of coronary artery plaques and to guide stent placement. Beyond ophthalmology and cardiology, applications are also developing in other medical specialties such as dermatology, gastroenterology (endoscopy), neurology, oncology, and dentistry.[22][23]

Introduction edit

 
Optical coherence tomogram of a fingertip. It is possible to observe the sweat glands, having "corkscrew appearance"

Interferometric reflectometry of biological tissue, especially of the human eye using short-coherence-length light (also referred to as partially-coherent, low-coherence, or broadband, broad-spectrum, or white light) was investigated in parallel by multiple groups worldwide since 1980s. In 1991, David Huang, then a student in James Fujimoto laboratory at Massachusetts Institute of Technology, working with Eric Swanson at the MIT Lincoln Laboratory and colleagues at the Harvard Medical School, successfully demonstrated imaging and called the new imaging modality "optical coherence tomography".[24] Since then, OCT with micrometer resolution and cross-sectional imaging capabilities has become a prominent biomedical imaging technique that has continually improved in technical performance and range of applications. The improvement in image acquisition rate is particularly spectacular, starting with the original 0.8 Hz axial scan repetition rate[1] to the current commercial clinical OCT systems operating at several hundred kHz and laboratory prototypes at multiple MHz. The range of applications has expanded from ophthalmology to cardiology and other medical specialties. For their roles in the invention of OCT, Fujimoto, Huang, and Swanson received the 2023 Lasker-DeBakey Clinical Medical Research Award and the National Medal of Technology and Innovation.[25] These developments have been reviewed in articles written for the general[21] scientific[26] and medical[27] readership.

It is particularly suited to ophthalmic applications and other tissue imaging requiring micrometer resolution and millimeter penetration depth.[28] OCT has also been used for various art conservation projects, where it is used to analyze different layers in a painting. OCT has interesting advantages over other medical imaging systems. Medical ultrasonography, magnetic resonance imaging (MRI), confocal microscopy, and OCT are differently suited to morphological tissue imaging: while the first two have whole body but low resolution imaging capability (typically a fraction of a millimeter), the third one can provide images with resolutions well below 1 micrometer (i.e. sub-cellular), between 0 and 100 micrometers in depth, and the fourth can probe as deep as 500 micrometers, but with a lower (i.e. architectural) resolution (around 10 micrometers in lateral and a few micrometers in depth in ophthalmology, for instance, and 20 micrometers in lateral in endoscopy).[29][30]

OCT is based on low-coherence interferometry.[31][32][33] In conventional interferometry with long coherence length (i.e., laser interferometry), interference of light occurs over a distance of meters. In OCT, this interference is shortened to a distance of micrometers, owing to the use of broad-bandwidth light sources (i.e., sources that emit light over a broad range of frequencies). Light with broad bandwidths can be generated by using superluminescent diodes or lasers with extremely short pulses (femtosecond lasers). White light is an example of a broadband source with lower power.

Light in an OCT system is broken into two arms – a sample arm (containing the item of interest) and a reference arm (usually a mirror). The combination of reflected light from the sample arm and reference light from the reference arm gives rise to an interference pattern, but only if light from both arms have traveled the "same" optical distance ("same" meaning a difference of less than a coherence length). By scanning the mirror in the reference arm, a reflectivity profile of the sample can be obtained (this is time domain OCT). Areas of the sample that reflect back a lot of light will create greater interference than areas that don't. Any light that is outside the short coherence length will not interfere.[34] This reflectivity profile, called an A-scan, contains information about the spatial dimensions and location of structures within the item of interest. A cross-sectional tomogram (B-scan) may be achieved by laterally combining a series of these axial depth scans (A-scan). A face imaging at an acquired depth is possible depending on the imaging engine used.

Layperson's explanation edit

 
Ocular OCT retinal thickness map, right eye
 
Time-domain OCT of the macular area of a retina at 800 nm, axial resolution 3 µm
 
Spectral-domain OCT macula cross-section scan.

Optical coherence tomography (OCT) is a technique for obtaining sub-surface images of translucent or opaque materials at a resolution equivalent to a low-power microscope. It is effectively "optical ultrasound", imaging reflections from within tissue to provide cross-sectional images.[35]

OCT has attracted interest among the medical community because it provides tissue morphology imagery at much higher resolution (less than 10 μm axially and less than 20 μm laterally[36] ) than other imaging modalities such as MRI or ultrasound.

The key benefits of OCT are:

  • Live sub-surface images at near-microscopic resolution
  • Instant, direct imaging of tissue morphology
  • No preparation of the sample or subject, no contact
  • No ionizing radiation

OCT delivers high resolution because it is based on light, rather than sound or radio frequency. An optical beam is directed at the tissue, and a small portion of this light that reflects from sub-surface features is collected. Note that most light is not reflected but, rather, scatters off at large angles. In conventional imaging, this diffusely scattered light contributes background that obscures an image. However, in OCT, a technique called interferometry is used to record the optical path length of received photons allowing rejection of most photons that scatter multiple times before detection. Thus OCT can build up clear 3D images of thick samples by rejecting background signal while collecting light directly reflected from surfaces of interest.

Within the range of noninvasive three-dimensional imaging techniques that have been introduced to the medical research community, OCT as an echo technique is similar to ultrasound imaging. Other medical imaging techniques such as computerized axial tomography, magnetic resonance imaging, or positron emission tomography do not use the echo-location principle.[37]

The technique is limited to imaging 1 to 2 mm below the surface in biological tissue, because at greater depths the proportion of light that escapes without scattering is too small to be detected. No special preparation of a biological specimen is required, and images can be obtained "non-contact" or through a transparent window or membrane. It is also important to note that the laser output from the instruments used is low – eye-safe near-infrared or visible-light[38] – and no damage to the sample is therefore likely.

Theory edit

The principle of OCT is white light, or low coherence, interferometry. The optical setup typically consists of an interferometer (Fig. 1, typically Michelson type) with a low coherence, broad bandwidth light source. Light is split into and recombined from reference and sample arms, respectively.

 
Fig. 1 Full-field OCT optical setup. Components include: super-luminescent diode (SLD), convex lens (L1), 50/50 beamsplitter (BS), camera objective (CO), CMOS-DSP camera (CAM), reference (REF), and sample (SMP). The camera functions as a two-dimensional detector array, and with the OCT technique facilitating scanning in depth, a non-invasive three-dimensional imaging device is achieved.
 
Fig. 2 Typical optical setup of single point OCT. Scanning the light beam on the sample enables non-invasive cross-sectional imaging up to 3 mm in depth with micrometer resolution.
 
Fig. 3 Spectral discrimination by swept-source OCT. Components include: swept source or tunable laser (SS), beamsplitter (BS), reference mirror (REF), sample (SMP), photodetector (PD), and digital signal processing (DSP)
 
Fig. 4 Spectral discrimination by Fourier-domain OCT. Components include: low coherence source (LCS), beamsplitter (BS), reference mirror (REF), sample (SMP), diffraction grating (DG) and full-field detector (CAM) acting as a spectrometer, and digital signal processing (DSP)

Time domain edit

 

In time domain OCT the path length of the reference arm is varied in time (the reference mirror is translated longitudinally). A property of low coherence interferometry is that interference, i.e. the series of dark and bright fringes, is only achieved when the path difference lies within the coherence length of the light source. This interference is called autocorrelation in a symmetric interferometer (both arms have the same reflectivity), or cross-correlation in the common case. The envelope of this modulation changes as path length difference is varied, where the peak of the envelope corresponds to path length matching.

The interference of two partially coherent light beams can be expressed in terms of the source intensity,  , as

 

where   represents the interferometer beam splitting ratio, and   is called the complex degree of coherence, i.e. the interference envelope and carrier dependent on reference arm scan or time delay  , and whose recovery is of interest in OCT. Due to the coherence gating effect of OCT the complex degree of coherence is represented as a Gaussian function expressed as[33]

 

where   represents the spectral width of the source in the optical frequency domain, and   is the centre optical frequency of the source. 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

 

where   is the central optical frequency of the source,   is the scanning velocity of the pathlength variation, and   is the speed of light.

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

   
 

where   and   are respectively the central wavelength and the spectral width of the light source.[39]

Fourier domain edit

 
interference signals in TD vs. FD-OCT

Fourier-domain (or Frequency-domain) OCT (FD-OCT) has speed and signal-to-noise ratio (SNR) advantages over time-domain OCT (TD-OCT) and has become the standard in the industry since 2006. The idea of using frequency modulation and coherent detection to obtain ranging information was already demonstrated in optical frequency domain reflectometry[9] and laser radar[14] in the 1980s, though the distance resolution and range were much longer than OCT. There are two types of FD-OCT – swept-source OCT (SS-OCT) and spectral-domain OCT (SD-OCT) – both of which acquire spectral interferograms which are then Fourier transformed to obtain an axial scan of reflectance amplitude versus depth. In SS-OCT, the spectral interferogram is acquired sequentially by tuning the wavelength of a laser light source. SD-OCT acquires spectral interferogram simultaneously in a spectrometer. An implementation of SS-OCT was described by the MIT group as early as 1994.[6][40]   A group based in the University of Vienna described measurement of intraocular distance using both tunable laser and spectrometer-based interferometry as early as 1995.[41][42] SD-OCT imaging was first demonstrated both in vitro and in vivo by a collaboration between the Vienna group and a group based in the Nicholas Copernicus University in a series of articles between 2000 and 2002.[43][44][45] The SNR advantage of FD-OCT over TD-OCT was analyzed by multiple groups of researchers in 2003.[46][47][48]

Spectral-domain OCT edit

Spectral-domain OCT (spatially encoded frequency domain OCT) extracts spectral information by distributing different optical frequencies onto a detector stripe (line-array CCD or CMOS) via a dispersive element (see Fig. 4). Thereby the information of the full depth scan can be acquired within a single exposure. However, the large signal-to-noise advantage of FD-OCT is reduced due to the lower dynamic range of stripe detectors with respect to single photosensitive diodes, resulting in an SNR advantage of ~10 dB at much higher speeds. This is not much of a problem when working at 1300 nm, however, since dynamic range is not a serious problem at this wavelength range.[39]

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 cannot 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.

Swept-source OCT edit

Swept-source OCT (Time-encoded frequency domain OCT) tries to combine some of the advantages of standard TD and spectral domain OCT. 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.e. frequency scanning laser) the optical setup (see Fig. 3) becomes simpler than spectral domain OCT, but the problem of scanning is essentially translated from the TD-OCT reference arm into the swept source OCT light source. Here the advantage lies in the proven high SNR detection technology, while swept laser sources achieve very small instantaneous bandwidths (linewidths) at very high frequencies (20–200 kHz). 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).

Scanning schemes edit

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).

Single point edit

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. 2). Two-dimensional lateral scanning has been electromechanically implemented by moving the sample[49] using a translation stage, and using a novel micro-electro-mechanical system scanner.[50]

Line-field OCT edit

Line-field confocal optical coherence tomography (LC-OCT) is an imaging technique based on the principle of time-domain OCT with line illumination using a broadband laser and line detection using a line-scan camera.[51] LC-OCT produces B-scans in real-time from multiple A-scans acquired in parallel. En face as well as three-dimensional images can also be obtained by scanning the illumination line laterally.[52][53] The focus is continuously adjusted during the scan of the sample depth, using a high numerical aperture (NA) microscope objective to image with high lateral resolution. By using a supercontinuum laser as a light source, a quasi-isotropic spatial resolution of ~ 1 µm is achieved at a central wavelength of ~ 800 nm. On the other hand, line illumination and detection, combined with the use of a high NA microscope objective, produce a confocal gate that prevents most scattered light that does not contribute to the signal from being detected by the camera. This confocal gate, which is absent in the full-field OCT technique, gives LC-OCT an advantage in terms of detection sensitivity and penetration in highly scattering media such as skin tissues.[54] So far this technique has been used mainly for skin imaging in the fields of dermatology[55][56][57][58][59][60] and cosmetology.[61]

Full-field OCT edit

 
Schematic view of a full-field OCT

An imaging approach to temporal OCT was developed by Claude Boccara's team in 1998,[62] with an acquisition of the images without beam scanning. In this technique called full-field OCT (FF-OCT), unlike other OCT techniques that acquire cross-sections of the sample, the images are here "en-face" i.e. like images of classical microscopy: orthogonal to the light beam of illumination.[63]

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 online) by the phase shift interferometry method, where usually 2 or 4 images per modulation period are acquired, depending on the algorithm used.[64][65] More recently, approaches that allow rapid single-shot imaging were developed to simultaneously capture multiple phase-shifted images required for reconstruction, using single camera.[66] Single-shot time-domain OCM is limited only by the camera frame rate and available illumination.

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.e. a broad spectrum), the spatial coherence must also be low to avoid parasitical interferences (i.e. a source with a large size).[67]

Selected applications edit

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.

Ophthalmology edit

Ocular (or ophthalmic) OCT is used heavily by ophthalmologists and optometrists to obtain high-resolution images of the retina and anterior segment. Owing to OCT's capability to show cross-sections of tissue layers with micrometer resolution, OCT provides a straightforward method of assessing cellular organization, photoreceptor integrity,[68][69][70][71] and axonal thickness in glaucoma,[72] macular degeneration,[73] diabetic macular edema,[74] multiple sclerosis,[75] optic neuritis,[76] and other eye diseases or systemic pathologies which have ocular signs.[77] Additionally, ophthalmologists leverage OCT to assess the vascular health of the retina via a technique called OCT angiography (OCTA).[78] In ophthalmological surgery, especially retinal surgery, an OCT can be mounted on the microscope. Such a system is called an intraoperative OCT (iOCT) and provides support during the surgery with clinical benefits.[79][80][81] Polarization-sensitive OCT was recently applied in the human retina to determine optical polarization properties of vessel walls near the optic nerve.[82]

Cardiology and neurovascular applications edit

In the settings of cardiology, OCT is used to image coronary arteries 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). For this type of application, 1 mm in diameter or smaller fiber-optics catheters are used to access artery lumen through semi-invasive interventions such as percutaneous coronary interventions.

The first demonstration of endoscopic OCT was reported in 1997, by researchers in James Fujimoto laboratory at Massachusetts Institute of Technology, including Guillermo James Tearney and Brett Bouma.[83] The first TD-OCT imaging catheter and system was commercialized by LightLab Imaging, Inc., a company based in Massachusetts in 2006. The first FD-OCT imaging study was reported by Massachusetts General Hospital in 2008.[84] Intracoronary FD-OCT was first introduced in the market in 2009 by LightLab Imaging, Inc.[85] followed by Terumo Corporation in 2012 and by Gentuity LLC in 2020.[86] The higher acquisition speed of FD-OCT enabled the widespread adoption of this imaging technology for coronary artery imaging. It is estimated that over 100,000 FD-OCT coronary imaging cases are performed yearly, and that the market is increasing by approximately 20% every year.[87]

Intravascular OCT has been further investigated for use in neurovascular applications including imaging for guiding endovascular treatment of ischemic stroke and brain aneurysms.[88] Clinical use of existing technologies has been limited to proximal intracranial anatomy of patient with limited tortuosity, however, it showed the potential of OCT for the imaging of neurovascular disease.[89] An intravascular OCT imaging catheter design tailored for use in tortuous neurovascular anatomy has been proposed in 2020.[90]

Further developments of intravascular OCT included the combination with other optical imaging modalities (multi-modality imaging). OCT has been combined with near-infrared fluorescence molecular imaging (NIRF) to enhance its capability to detect molecular/functional and tissue morphological information simultaneously.[91][92] In a similar way, combination with near-infrared spectroscopy (NIRS) has been implemented.[93]

Retinal imaging with PS-OCT demonstrated how the thickness and birefringence of blood vessel wall tissue of healthy subjects could be quantified, in vivo.[94] PS-OCT was subsequently applied to patients with diabetes and age-matched healthy subjects, and showed an almost 100% increase in vessel wall birefringence due to diabetes, without a significant change in vessel wall thickness.[95] In patients with hypertension however, the retinal vessel wall thickness increased by 60% while the vessel wall birefringence dropped by 20%, on average.[96] The large differences measured in healthy subjects and patients suggest that retinal measurements with PS-OCT could be used as a screening tool for hypertension and diabetes.[95][96][97]

Oncology edit

Endoscopic OCT has been applied to the detection and diagnosis of cancer and precancerous lesions, such as Barrett's esophagus and esophageal dysplasia.[98][99][100]

Dermatology edit

The first use of OCT in dermatology dates back to 1997.[101] Since then, OCT has been applied to the diagnosis of various skin lesions including carcinomas.[102][103][104] However, the diagnosis of melanoma using conventional OCT is difficult, especially due to insufficient imaging resolution.[105] Emerging high-resolution OCT techniques such as LC-OCT have the potential to improve the clinical diagnostic process, allowing for the early detection of malignant skin tumors – including melanoma – and a reduction in the number of surgical excisions of benign lesions.[106] Other promising areas of application include the imaging of lesions where excisions are hazardous or impossible and the guidance of surgical interventions through identification of tumor margins.

Dentistry edit

Researchers in Tokyo medical and Dental University were able to detect enamel white spot lesions around and beneath the orthodontic brackets using swept source OCT.[107]

Research applications edit

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.[108][109] Optical coherence tomography is also applicable and increasingly used in industrial applications, such as nondestructive testing (NDT), material thickness measurements,[110] and in particular thin silicon wafers[111][112] and compound semiconductor wafers thickness measurements[113][114] surface roughness characterization, surface and cross-section imaging[115][116] and volume loss measurements.[117] OCT systems with feedback can be used to control manufacturing processes. With high speed data acquisition,[118] and sub-micron resolution, OCT is adaptable to perform both inline and off-line.[119] Due to the high volume of produced pills, an interesting field of application is in the pharmaceutical industry to control the coating of tablets.[120] Fiber-based OCT systems are particularly adaptable to industrial environments.[121] These can access and scan interiors of hard-to-reach spaces,[122] and are able to operate in hostile environments—whether radioactive, cryogenic, or very hot.[123] Novel optical biomedical diagnostic and imaging technologies are currently being developed to solve problems in biology and medicine.[124] As of 2014, attempts have been made to use optical coherence tomography to identify root canals in teeth, specifically canal in the maxillary molar, however, there is no difference with the current methods of dental operatory microscope.[125][126][non-primary source needed] Research conducted in 2015 was successful in utilizing a smartphone as an OCT platform, although much work remains to be done before such a platform would be commercially viable.[127] Photonic integrated circuits may be a promising option to miniaturized OCT. Similarly to integrated circuits silicon-based fabrication techniques can be used to produce miniaturized photonic systems. First in vivo human retinal imaging has been reported recently.[128] In 3D microfabrication, OCT enables non-destructive testing and real-time inspection during additive manufacturing. Its high-resolution imaging detects defects, characterizes material properties and ensures the integrity of internal geometries without damaging the part.[117]

See also edit

References edit

  1. ^ a b Huang D, Swanson EA, Lin CP, Schuman JS, Stinson WG, Chang W, et al. (November 1991). "Optical coherence tomography". Science. 254 (5035): 1178–1181. Bibcode:1991Sci...254.1178H. doi:10.1126/science.1957169. PMC 4638169. PMID 1957169.
  2. ^ Youngquist RC, Carr S, Davies DE (March 1987). "Optical coherence-domain reflectometry: a new optical evaluation technique". Optics Letters. 12 (3): 158–160. Bibcode:1987OptL...12..158Y. doi:10.1364/ol.12.000158. PMID 19738824.
  3. ^ Izatt JA, Hee MR, Huang D, Fujimoto JG, Swanson EA, Lin CP, Shuman JS, Puliafito CA (1993-06-24). Parel JM, Ren Q (eds.). "Ophthalmic diagnostics using optical coherence tomography". Ophthalmic Technologies III. SPIE. 1877: 136–144. Bibcode:1993SPIE.1877..136I. doi:10.1117/12.147520. S2CID 121094027.
  4. ^ Swanson EA, Izatt JA, Hee MR, Huang D, Lin CP, Schuman JS, et al. (November 1993). "In vivo retinal imaging by optical coherence tomography". Optics Letters. 18 (21): 1864–1866. Bibcode:1993OptL...18.1864S. doi:10.1364/ol.18.001864. PMID 19829430.
  5. ^ Fercher AF, Hitzenberger CK, Drexler W, Kamp G, Sattmann H (July 1993). "In vivo optical coherence tomography". American Journal of Ophthalmology. 116 (1): 113–114. doi:10.1016/s0002-9394(14)71762-3. PMID 8328536.
  6. ^ a b c US 5321501A, Swanson EA, Huang D, Fujimoto JG, Puliafito CA, "Method and apparatus for optical imaging with means for controlling the longitudinal range of the sample", issued 1994-06-14 
  7. ^ US 5459570A, Swanson EA, Huang D, Fujimoto JG, Puliafito CA, "Method and apparatus for performing optical measurements", issued 1995-10-17 
  8. ^ JA 2010042, Tanno N, Ichikawa T, Saeki A, "Lightwave Reflection Measurement", published 1990 
  9. ^ a b Eickhoff W, Ulrich R (November 1981). "Optical frequency domain reflectometry in single-mode fiber". Applied Physics Letters. 39 (9): 693–695. Bibcode:1981ApPhL..39..693E. doi:10.1063/1.92872. ISSN 0003-6951.
  10. ^ Gillard CW, Buholz NE (1983). "Progress In Absolute Distance Interferometry". Optical Engineering. 22 (3): 348–353. Bibcode:1983OptEn..22..348G. doi:10.1117/12.7973117. ISSN 0091-3286.
  11. ^ Fercher AF, Roth E (1986-09-15). Mueller GJ (ed.). "Ophthalmic Laser Interferometry". SPIE Proceedings. Optical Instrumentation for Biomedical Laser Applications. SPIE. 0658: 48. Bibcode:1986SPIE..658...48F. doi:10.1117/12.938523. S2CID 122883903.
  12. ^ Youngquist RC, Carr S, Davies DE (March 1987). "Optical coherence-domain reflectometry: a new optical evaluation technique". Optics Letters. 12 (3): 158–160. Bibcode:1987OptL...12..158Y. doi:10.1364/OL.12.000158. PMID 19738824.
  13. ^ Takada K, Yokohama I, Chida K, Noda J (May 1987). "New measurement system for fault location in optical waveguide devices based on an interferometric technique". Applied Optics. 26 (9): 1603–1606. Bibcode:1987ApOpt..26.1603T. doi:10.1364/AO.26.001603. PMID 20454375.
  14. ^ a b Kachelmyer AL (1989-02-18). Becherer RJ (ed.). "Range-Doppler Imaging Waveforms And Receiver Design". Laser Radar III. SPIE. 0999: 138–161. Bibcode:1989SPIE..999..138K. doi:10.1117/12.960231. S2CID 110631959.
  15. ^ Fercher AF, Mengedoht K, Werner W (March 1988). "Eye-length measurement by interferometry with partially coherent light". Optics Letters. 13 (3): 186–188. Bibcode:1988OptL...13..186F. doi:10.1364/OL.13.000186. PMID 19742022.
  16. ^ Gilgen HH, Novak RP, Salathe RP, Hodel W, Beaud P (1989). "Submillimeter optical reflectometry". Journal of Lightwave Technology. 7 (8): 1225–1233. Bibcode:1989JLwT....7.1225G. doi:10.1109/50.32387. ISSN 1558-2213.
  17. ^ Huang D, Wang J, Lin CP, Puliafito CA, Fujimoto JG (1991). "Micron-resolution ranging of cornea anterior chamber by optical reflectometry". Lasers in Surgery and Medicine. 11 (5): 419–425. doi:10.1002/lsm.1900110506. PMID 1816476. S2CID 19888483.
  18. ^ Hitzenberger CK (March 1991). "Optical measurement of the axial eye length by laser Doppler interferometry". Investigative Ophthalmology & Visual Science. 32 (3): 616–624. PMID 2001935.
  19. ^ a b Fercher AF (12–16 August 1990). "Ophthalmic interferometry". In von Bally G, Khanna S (eds.). Proceedings of the International Conference on Optics in Life Sciences. Garmisch-Partenkirchen, Germany. pp. 221–228. ISBN 0-444-89860-3.
  20. ^ a b Shinji Chiba; Naohiro Tanno (1991). Backscattering Optical Heterodyne Tomography. 14th Laser Sensing Symposium (in Japanese).
  21. ^ a b Fujimoto J, Swanson E (July 2016). "The Development, Commercialization, and Impact of Optical Coherence Tomography". Investigative Ophthalmology & Visual Science. 57 (9): OCT1–OCT13. doi:10.1167/iovs.16-19963. PMC 4968928. PMID 27409459.
  22. ^ Wijns W, Shite J, Jones MR, Lee SW, Price MJ, Fabbiocchi F, et al. (December 2015). "Optical coherence tomography imaging during percutaneous coronary intervention impacts physician decision-making: ILUMIEN I study". European Heart Journal. 36 (47): 3346–3355. doi:10.1093/eurheartj/ehv367. PMC 4677272. PMID 26242713.
  23. ^ Fujimoto J, Huang D (July 2016). "Foreword: 25 Years of Optical Coherence Tomography". Investigative Ophthalmology & Visual Science. 57 (9): OCTi–OCTii. doi:10.1167/iovs.16-20269. PMID 27419359.
  24. ^ Huang D, Swanson EA, Lin CP, Schuman JS, Stinson WG, Chang W, et al. (November 1991). "Optical coherence tomography". Science. 254 (5035): 1178–1181. Bibcode:1991Sci...254.1178H. doi:10.1126/science.1957169. PMC 4638169. PMID 1957169.
  25. ^ Davis TH (September 2023). "QnAs with James G. Fujimoto, David Huang, and Eric A. Swanson: Winners of the 2023 Lasker~DeBakey Clinical Medical Research Award". Proceedings of the National Academy of Sciences of the United States of America. 120 (39): e2313883120. Bibcode:2023PNAS..12013883D. doi:10.1073/pnas.2313883120. PMC 10523481. PMID 37732757.
  26. ^ Nathans J (September 2023). "Seeing is believing: The development of optical coherence tomography". Proceedings of the National Academy of Sciences of the United States of America. 120 (39): e2311129120. Bibcode:2023PNAS..12011129N. doi:10.1073/pnas.2311129120. PMC 10523475. PMID 37732756.
  27. ^ Toth CA (October 2023). Phimister EG (ed.). "Optical Coherence Tomography and Eye Care". The New England Journal of Medicine. 389 (16): 1526–1529. doi:10.1056/NEJMcibr2307733. PMID 37732605. S2CID 262085371.
  28. ^ Zysk AM, Nguyen FT, Oldenburg AL, Marks DL, Boppart SA (2007). "Optical coherence tomography: a review of clinical development from bench to bedside". Journal of Biomedical Optics. 12 (5): 051403. Bibcode:2007JBO....12e1403Z. doi:10.1117/1.2793736. PMID 17994864. S2CID 20621284.
  29. ^ Drexler W, Morgner U, Ghanta RK, Kärtner FX, Schuman JS, Fujimoto JG (April 2001). "Ultrahigh-resolution ophthalmic optical coherence tomography". Nature Medicine. 7 (4): 502–507. doi:10.1038/86589. PMC 1950821. PMID 11283681.
  30. ^ Kaufman SC, Musch DC, Belin MW, Cohen EJ, Meisler DM, Reinhart WJ, et al. (February 2004). "Confocal microscopy: a report by the American Academy of Ophthalmology". Ophthalmology. 111 (2): 396–406. doi:10.1016/j.ophtha.2003.12.002. PMID 15019397.
  31. ^ Riederer SJ (2000). "Current technical development of magnetic resonance imaging". IEEE Engineering in Medicine and Biology Magazine. 19 (5): 34–41. doi:10.1109/51.870229. PMID 11016028.
  32. ^ M. Born; E. Wolf (2000). Principles of Optics: Electromagnetic Theory of Propagation, Interference, and Diffraction of Light. Cambridge University Press. ISBN 978-0-521-78449-8.
  33. ^ a b Fercher AF, Mengedoht K, Werner W (March 1988). "Eye-length measurement by interferometry with partially coherent light". Optics Letters. 13 (3): 186–188. Bibcode:1988OptL...13..186F. doi:10.1364/OL.13.000186. PMID 19742022.
  34. ^ Fujimoto JG, Pitris C, Boppart SA, Brezinski ME (2000). "Optical coherence tomography: an emerging technology for biomedical imaging and optical biopsy". Neoplasia. 2 (1–2): 9–25. doi:10.1038/sj.neo.7900071. PMC 1531864. PMID 10933065.
  35. ^ Michelessi M, Lucenteforte E, Oddone F, Brazzelli M, Parravano M, Franchi S, et al. (November 2015). "Optic nerve head and fibre layer imaging for diagnosing glaucoma". The Cochrane Database of Systematic Reviews. 2015 (11): CD008803. doi:10.1002/14651858.CD008803.pub2. PMC 4732281. PMID 26618332.
  36. ^ Drexler W, Morgner U, Kärtner FX, Pitris C, Boppart SA, Li XD, et al. (September 1999). "In vivo ultrahigh-resolution optical coherence tomography". Optics Letters. OSA. 24 (17): 1221–1223. doi:10.1364/bio.1999.jwa2. PMID 18073990.
  37. ^ "Optical Coherence Tomography provides better resolution than an MRI and Helps Diagnose Retina & Corneal Disease and Glaucoma, Part II". mastereyeassociates.com. mastereyeassociates. June 13, 2017. Retrieved June 13, 2017.
  38. ^ Shu X, Beckmann L, Zhang H (December 2017). "Visible-light optical coherence tomography: a review". Journal of Biomedical Optics. spiedigitallibrary. 22 (12): 1–14. Bibcode:2017JBO....22l1707S. doi:10.1117/1.JBO.22.12.121707. PMC 5745673. PMID 29218923.
  39. ^ a b Garg A (2014). Anterior & Posterior Segment OCT: Current Technology & Future Applications, 1st edition.
  40. ^ Chinn SR, Swanson EA, Fujimoto JG (March 1997). "Optical coherence tomography using a frequency-tunable optical source". Optics Letters. 22 (5): 340–342. Bibcode:1997OptL...22..340C. doi:10.1364/OL.22.000340. PMID 18183195.
  41. ^ Fercher AF, Hitzenberger CK, Kamp G, El-Zaiat SY (1995-05-15). "Measurement of intraocular distances by backscattering spectral interferometry". Optics Communications. 117 (1): 43–48. Bibcode:1995OptCo.117...43F. doi:10.1016/0030-4018(95)00119-S. ISSN 0030-4018.
  42. ^ Lexer F, Hitzenberger CK, Fercher AF, Kulhavy M (September 1997). "Wavelength-tuning interferometry of intraocular distances". Applied Optics. 36 (25): 6548–6553. Bibcode:1997ApOpt..36.6548L. doi:10.1364/AO.36.006548. PMID 18259516.
  43. ^ Leitgeb R, Wojtkowski M, Kowalczyk A, Hitzenberger CK, Sticker M, Fercher AF (June 2000). "Spectral measurement of absorption by spectroscopic frequency-domain optical coherence tomography". Optics Letters. 25 (11): 820–822. Bibcode:2000OptL...25..820L. doi:10.1364/OL.25.000820. PMID 18064195.
  44. ^ Wojtkowski M, Leitgeb R, Kowalczyk A, Bajraszewski T, Fercher AF (July 2002). "In vivo human retinal imaging by Fourier domain optical coherence tomography". Journal of Biomedical Optics. 7 (3): 457–463. Bibcode:2002JBO.....7..457W. doi:10.1117/1.1482379. PMID 12175297. S2CID 40844236.
  45. ^ Wojtkowski M, Kowalczyk A, Leitgeb R, Fercher AF (August 2002). "Full range complex spectral optical coherence tomography technique in eye imaging". Optics Letters. 27 (16): 1415–1417. Bibcode:2002OptL...27.1415W. doi:10.1364/OL.27.001415. PMID 18026464.
  46. ^ Leitgeb R, Hitzenberger C, Fercher A (April 2003). "Performance of fourier domain vs. time domain optical coherence tomography". Optics Express. 11 (8): 889–894. Bibcode:2003OExpr..11..889L. doi:10.1364/oe.11.000889. PMID 19461802.
  47. ^ Choma M, Sarunic M, Yang C, Izatt J (September 2003). "Sensitivity advantage of swept source and Fourier domain optical coherence tomography". Optics Express. 11 (18): 2183–2189. Bibcode:2003OExpr..11.2183C. doi:10.1364/oe.11.002183. PMID 19466106.
  48. ^ de Boer JF, Cense B, Park BH, Pierce MC, Tearney GJ, Bouma BE (November 2003). "Improved signal-to-noise ratio in spectral-domain compared with time-domain optical coherence tomography". Optics Letters. 28 (21): 2067–2069. Bibcode:2003OptL...28.2067D. doi:10.1364/ol.28.002067. PMID 14587817.
  49. ^ Fercher AF, Hitzenberger CK, Kamp G, El-Zaiat SY (1995). "Measurement of intraocular distances by backscattering spectral interferometry". Optics Communications. 117 (1–2): 43–48. Bibcode:1995OptCo.117...43F. doi:10.1016/0030-4018(95)00119-S.
  50. ^ Yeow JT, Yang VX, Chahwan A, Gordon ML, Qi B, Vitkin IA, Wilson BC, Goldenberg AA (2005). "Micromachined 2-D scanner for 3-D optical coherence tomography". Sensors and Actuators A: Physical. 117 (2): 331–340. doi:10.1016/j.sna.2004.06.021.
  51. ^ Dubois A, Levecq O, Azimani H, Davis A, Ogien J, Siret D, Barut A (December 2018). "Line-field confocal time-domain optical coherence tomography with dynamic focusing". Optics Express. 26 (26): 33534–33542. Bibcode:2018OExpr..2633534D. doi:10.1364/OE.26.033534. PMID 30650800.
  52. ^ Ogien J, Levecq O, Azimani H, Dubois A (March 2020). "Dual-mode line-field confocal optical coherence tomography for ultrahigh-resolution vertical and horizontal section imaging of human skin in vivo". Biomedical Optics Express. 11 (3): 1327–1335. doi:10.1364/BOE.385303. PMC 7075601. PMID 32206413.
  53. ^ Ogien J, Daures A, Cazalas M, Perrot JL, Dubois A (December 2020). "Line-field confocal optical coherence tomography for three-dimensional skin imaging". Frontiers of Optoelectronics. 13 (4): 381–392. doi:10.1007/s12200-020-1096-x. PMC 9743950. PMID 36641566. S2CID 234456595.
  54. ^ Chen Y, Huang SW, Aguirre AD, Fujimoto JG (July 2007). "High-resolution line-scanning optical coherence microscopy". Optics Letters. 32 (14): 1971–1973. Bibcode:2007OptL...32.1971C. doi:10.1364/OL.32.001971. PMID 17632613.
  55. ^ Dubois A, Levecq O, Azimani H, Siret D, Barut A, Suppa M, et al. (October 2018). "Line-field confocal optical coherence tomography for high-resolution noninvasive imaging of skin tumors". Journal of Biomedical Optics. 23 (10): 1–9. Bibcode:2018JBO....23j6007D. doi:10.1117/1.JBO.23.10.106007. PMID 30353716.
  56. ^ Ruini C, Schuh S, Gust C, Kendziora B, Frommherz L, French LE, et al. (December 2021). "Line-field optical coherence tomography: in vivo diagnosis of basal cell carcinoma subtypes compared with histopathology". Clinical and Experimental Dermatology. 46 (8): 1471–1481. doi:10.1111/ced.14762. hdl:11380/1259112. PMID 34047380. S2CID 235232158.
  57. ^ Suppa M, Fontaine M, Dejonckheere G, Cinotti E, Yélamos O, Diet G, et al. (May 2021). "Line-field confocal optical coherence tomography of basal cell carcinoma: a descriptive study". Journal of the European Academy of Dermatology and Venereology. 35 (5): 1099–1110. doi:10.1111/jdv.17078. PMID 33398911. S2CID 230583854.
  58. ^ Cinotti E, Tognetti L, Cartocci A, Lamberti A, Gherbassi S, Orte Cano C, et al. (December 2021). "Line-field confocal optical coherence tomography for actinic keratosis and squamous cell carcinoma: a descriptive study". Clinical and Experimental Dermatology. 46 (8): 1530–1541. doi:10.1111/ced.14801. PMC 9293459. PMID 34115900. S2CID 235411841.
  59. ^ Lenoir C, Cinotti E, Tognetti L, Orte Cano C, Diet G, Miyamoto M, et al. (December 2021). "Line-field confocal optical coherence tomography of actinic keratosis: a case series". Journal of the European Academy of Dermatology and Venereology. 35 (12): e900–e902. doi:10.1111/jdv.17548. PMID 34310768. S2CID 236452537.
  60. ^ Ruini C, Schuh S, Gust C, Kendziora B, Frommherz L, French LE, et al. (December 2021). "Line-field confocal optical coherence tomography for the in vivo real-time diagnosis of different stages of keratinocyte skin cancer: a preliminary study". Journal of the European Academy of Dermatology and Venereology. 35 (12): 2388–2397. doi:10.1111/jdv.17603. hdl:11380/1259110. PMID 34415646. S2CID 237241412.
  61. ^ Pedrazzani M, Breugnot J, Rouaud-Tinguely P, Cazalas M, Davis A, Bordes S, et al. (May 2020). "Comparison of line-field confocal optical coherence tomography images with histological sections: Validation of a new method for in vivo and non-invasive quantification of superficial dermis thickness". Skin Research and Technology. 26 (3): 398–404. doi:10.1111/srt.12815. PMID 31799766. S2CID 208622348.
  62. ^ Beaurepaire E, Boccara AC, Lebec M, Blanchot L, Saint-Jalmes H (February 1998). "Full-field optical coherence microscopy". Optics Letters. 23 (4): 244–246. Bibcode:1998OptL...23..244B. doi:10.1364/ol.23.000244. PMID 18084473.
  63. ^ Dubois A, Boccara C (October 2006). "[Full-field OCT]". Médecine/Sciences (in French). 22 (10): 859–864. doi:10.1051/medsci/20062210859. PMID 17026940.
  64. ^ Dubois A, Moneron G, Boccara C (2006). "Thermal-light full-field optical coherence tomography in the 1.2 micron wavelength region" (PDF). Optics Communications. 266 (2): 738–743. Bibcode:2006OptCo.266..738D. doi:10.1016/j.optcom.2006.05.016. S2CID 120323507.
  65. ^ Boccara AC, Harms F, Latrive A (2013). "Full-field OCT: a non-invasive tool for diagnosis and tissue selection". SPIE Newsroom. doi:10.1117/2.1201306.004933. S2CID 123478275.
  66. ^ Žurauskas M, Iyer RR, Boppart SA (February 2021). "Simultaneous 4-phase-shifted full-field optical coherence microscopy". Biomedical Optics Express. The Optical Society. 12 (2): 981–992. doi:10.1364/boe.417183. PMC 7901320. PMID 33680554.
  67. ^ Boccara AC, Dubois A (2013). "Optical Coherence Tomography". Optics in Instruments. pp. 101–123. doi:10.1002/9781118574386.ch3. ISBN 9781118574386.
  68. ^ "The ABCs of OCT". Review of Optometry.
  69. ^ Sherman J (June 2009). "Photoreceptor integrity line joins the nerve fiber layer as key to clinical diagnosis". Optometry. 80 (6): 277–278. doi:10.1016/j.optm.2008.12.006. PMID 19465337.
  70. ^ "Outer Retinal Layers as Predictors of Vision Loss". Review of Ophthalmology.
  71. ^ Cuenca N, Ortuño-Lizarán I, Pinilla I (March 2018). "Cellular Characterization of OCT and Outer Retinal Bands Using Specific Immunohistochemistry Markers and Clinical Implications". Ophthalmology. 125 (3): 407–422. doi:10.1016/j.ophtha.2017.09.016. hdl:10045/74474. PMID 29037595.
  72. ^ Grewal DS, Tanna AP (March 2013). "Diagnosis of glaucoma and detection of glaucoma progression using spectral domain optical coherence tomography". Current Opinion in Ophthalmology. 24 (2): 150–161. doi:10.1097/ICU.0b013e32835d9e27. PMID 23328662. S2CID 39039199.
  73. ^ Keane PA, Patel PJ, Liakopoulos S, Heussen FM, Sadda SR, Tufail A (September 2012). "Evaluation of age-related macular degeneration with optical coherence tomography". Survey of Ophthalmology. 57 (5): 389–414. doi:10.1016/j.survophthal.2012.01.006. PMID 22898648.
  74. ^ Virgili G, Menchini F, Casazza G, Hogg R, Das RR, Wang X, Michelessi M (January 2015). "Optical coherence tomography (OCT) for detection of macular oedema in patients with diabetic retinopathy". The Cochrane Database of Systematic Reviews. 1: CD008081. doi:10.1002/14651858.CD008081.pub3. PMC 4438571. PMID 25564068.
  75. ^ Dörr J, Wernecke KD, Bock M, Gaede G, Wuerfel JT, Pfueller CF, et al. (April 2011). "Association of retinal and macular damage with brain atrophy in multiple sclerosis". PLOS ONE. 6 (4): e18132. Bibcode:2011PLoSO...618132D. doi:10.1371/journal.pone.0018132. PMC 3072966. PMID 21494659.  
  76. ^ Petzold A, Fraser CL, Abegg M, Alroughani R, Alshowaeir D, Alvarenga R, et al. (December 2022). "Diagnosis and classification of optic neuritis". The Lancet. Neurology. 21 (12): 1120–1134. doi:10.1016/s1474-4422(22)00200-9. PMID 36179757. S2CID 252564095.
  77. ^ Aik Kah T (2018). "CuRRL Syndrome: A Case Series" (PDF). Acta Scientific Ophthalmology. 1: 9–13.
  78. ^ Kashani AH, Chen CL, Gahm JK, Zheng F, Richter GM, Rosenfeld PJ, et al. (September 2017). "Optical coherence tomography angiography: A comprehensive review of current methods and clinical applications". Progress in Retinal and Eye Research. 60: 66–100. doi:10.1016/j.preteyeres.2017.07.002. PMC 5600872. PMID 28760677.
  79. ^ Ehlers JP, Tao YK, Srivastava SK (May 2014). "The value of intraoperative optical coherence tomography imaging in vitreoretinal surgery". Current Opinion in Ophthalmology. 25 (3): 221–227. doi:10.1097/ICU.0000000000000044. PMC 4119822. PMID 24614147.
  80. ^ Pfau M, Michels S, Binder S, Becker MD (2015). "Clinical Experience With the First Commercially Available Intraoperative Optical Coherence Tomography System". Ophthalmic Surgery, Lasers & Imaging Retina. 46 (10): 1001–1008. doi:10.3928/23258160-20151027-03. PMID 26599241.
  81. ^ Neuhann R, Neuhann T, Hörster R, Cursiefen C, Guell J, Siebelmann S (December 2021). "Laser-integrated real-time OCT in anterior segment procedures". Journal of Cataract and Refractive Surgery. 47 (12): e88–e92. doi:10.1097/j.jcrs.0000000000000773. PMID 34393183.
  82. ^ Neuhann R, Neuhann T, Hörster R, Cursiefen C, Guell J, Siebelmann S (December 2021). "Laser-integrated real-time OCT in anterior segment procedures". Journal of Cataract and Refractive Surgery. 47 (12): e88–e92. doi:10.1364/BOE.426079. PMC 8367251. PMID 34393183.
  83. ^ Tearney GJ, Brezinski ME, Bouma BE, Boppart SA, Pitris C, Southern JF, Fujimoto JG (June 1997). "In vivo endoscopic optical biopsy with optical coherence tomography". Science. 276 (5321): 2037–2039. doi:10.1126/science.276.5321.2037. PMID 9197265. S2CID 43035300.
  84. ^ Tearney GJ, Waxman S, Shishkov M, Vakoc BJ, Suter MJ, Freilich MI, et al. (November 2008). "Three-dimensional coronary artery microscopy by intracoronary optical frequency domain imaging". JACC. Cardiovascular Imaging. 1 (6): 752–761. doi:10.1016/j.jcmg.2008.06.007. PMC 2852244. PMID 19356512.
  85. ^ "LightLab launches FD-OCT in Europe" (Press release). Retrieved 9 September 2016.
  86. ^ Bezerra HG, Quimby DL, Matar F, Mohanty BD, Bassily E, Ughi GJ (July 2023). "High-Frequency Optical Coherence Tomography (HF-OCT) for Preintervention Coronary Imaging: A First-in-Human Study". JACC. Cardiovascular Imaging. 16 (7): 982–984. doi:10.1016/j.jcmg.2023.01.013. PMID 37407126. S2CID 258115402.
  87. ^ Swanson E (13 June 2016). "Optical Coherence Tomography: Beyond better clinical care: OCT's economic impact". BioOptics World. Retrieved 9 September 2016.
  88. ^ Chen CJ, Kumar JS, Chen SH, Ding D, Buell TJ, Sur S, et al. (April 2018). "Optical Coherence Tomography: Future Applications in Cerebrovascular Imaging". Stroke. 49 (4): 1044–1050. doi:10.1161/STROKEAHA.117.019818. PMID 29491139.
  89. ^ Xu X, Li M, Liu R, Yin Q, Shi X, Wang F, et al. (August 2020). "Optical coherence tomography evaluation of vertebrobasilar artery stenosis: case series and literature review". Journal of Neurointerventional Surgery. 12 (8): 809–813. doi:10.1136/neurintsurg-2019-015660. PMID 32066569. S2CID 211159079.
  90. ^ Ughi GJ, Marosfoi MG, King RM, Caroff J, Peterson LM, Duncan BH, et al. (July 2020). "A neurovascular high-frequency optical coherence tomography system enables in situ cerebrovascular volumetric microscopy". Nature Communications. 11 (1): 3851. Bibcode:2020NatCo..11.3851U. doi:10.1038/s41467-020-17702-7. PMC 7395105. PMID 32737314.
  91. ^ Ughi GJ, Wang H, Gerbaud E, Gardecki JA, Fard AM, Hamidi E, et al. (November 2016). "Clinical Characterization of Coronary Atherosclerosis With Dual-Modality OCT and Near-Infrared Autofluorescence Imaging". JACC. Cardiovascular Imaging. 9 (11): 1304–1314. doi:10.1016/j.jcmg.2015.11.020. PMC 5010789. PMID 26971006.
  92. ^ Hara T, Ughi GJ, McCarthy JR, Erdem SS, Mauskapf A, Lyon SC, et al. (February 2017). "Intravascular fibrin molecular imaging improves the detection of unhealed stents assessed by optical coherence tomography in vivo". European Heart Journal. 38 (6): 447–455. doi:10.1093/eurheartj/ehv677. PMC 5837565. PMID 26685129.
  93. ^ Fard AM, Vacas-Jacques P, Hamidi E, Wang H, Carruth RW, Gardecki JA, Tearney GJ (December 2013). "Optical coherence tomography--near infrared spectroscopy system and catheter for intravascular imaging". Optics Express. 21 (25): 30849–30858. Bibcode:2013OExpr..2130849F. doi:10.1364/OE.21.030849. PMC 3926541. PMID 24514658.
  94. ^ Afsharan, Hadi; Hackmann, Michael J.; Wang, Qiang; Navaeipour, Farzaneh; Jayasree, Stephy Vijaya Kumar; Zawadzki, Robert J.; Silva, Dilusha; Joo, Chulmin; Cense, Barry (2021-07-01). "Polarization properties of retinal blood vessel walls measured with polarization sensitive optical coherence tomography". Biomedical Optics Express. 12 (7): 4340–4362. doi:10.1364/BOE.426079. ISSN 2156-7085. PMC 8367251. PMID 34457418.
  95. ^ a b Afsharan, Hadi; Silva, Dilusha; Joo, Chulmin; Cense, Barry (August 2023). "Non-Invasive Retinal Blood Vessel Wall Measurements with Polarization-Sensitive Optical Coherence Tomography for Diabetes Assessment: A Quantitative Study". Biomolecules. 13 (8): 1230. doi:10.3390/biom13081230. ISSN 2218-273X. PMC 10452597. PMID 37627295.
  96. ^ a b Afsharan, Hadi; Anilkumar, Vidyalakshmi; Silva, Dilusha; Dwivedi, Girish; Joo, Chulmin; Cense, Barry (2024-01-01). "Hypertension-associated changes in retinal blood vessel walls measured in vivo with polarization-sensitive optical coherence tomography". Optics and Lasers in Engineering. 172: 107838. Bibcode:2024OptLE.17207838A. doi:10.1016/j.optlaseng.2023.107838. ISSN 0143-8166.
  97. ^ "Basic eye test could diagnose diabetes and hypertension". PerthNow. 2023-09-20. Retrieved 2024-01-24.
  98. ^ "Next-gen OCT for the esophagus". BioOptics World. 1 May 2013. Retrieved 9 September 2016.
  99. ^ Gora MJ, Sauk JS, Carruth RW, Gallagher KA, Suter MJ, Nishioka NS, et al. (February 2013). "Tethered capsule endomicroscopy enables less invasive imaging of gastrointestinal tract microstructure". Nature Medicine. 19 (2): 238–240. doi:10.1038/nm.3052. PMC 3567218. PMID 23314056.
  100. ^ Ughi GJ, Gora MJ, Swager AF, Soomro A, Grant C, Tiernan A, et al. (February 2016). "Automated segmentation and characterization of esophageal wall in vivo by tethered capsule optical coherence tomography endomicroscopy". Biomedical Optics Express. 7 (2): 409–419. doi:10.1364/BOE.7.000409. PMC 4771459. PMID 26977350.
  101. ^ Welzel J, Lankenau E, Birngruber R, Engelhardt R (December 1997). "Optical coherence tomography of the human skin". Journal of the American Academy of Dermatology. 37 (6): 958–963. doi:10.1016/S0190-9622(97)70072-0. PMID 9418764. S2CID 20078741.
  102. ^ Boone MA, Norrenberg S, Jemec GB, Del Marmol V (October 2012). "Imaging of basal cell carcinoma by high-definition optical coherence tomography: histomorphological correlation. A pilot study". The British Journal of Dermatology. 167 (4): 856–864. doi:10.1111/j.1365-2133.2012.11194.x. PMID 22862425. S2CID 24965088.
  103. ^ Coleman AJ, Richardson TJ, Orchard G, Uddin A, Choi MJ, Lacy KE (February 2013). "Histological correlates of optical coherence tomography in non-melanoma skin cancer". Skin Research and Technology. 19 (1): 10–19. doi:10.1111/j.1600-0846.2012.00626.x. PMID 22738357. S2CID 26084419.
  104. ^ Ulrich M, von Braunmuehl T, Kurzen H, Dirschka T, Kellner C, Sattler E, et al. (August 2015). "The sensitivity and specificity of optical coherence tomography for the assisted diagnosis of nonpigmented basal cell carcinoma: an observational study". The British Journal of Dermatology. 173 (2): 428–435. doi:10.1111/bjd.13853. PMID 25904111.
  105. ^ Levine A, Wang K, Markowitz O (October 2017). "Optical Coherence Tomography in the Diagnosis of Skin Cancer". Dermatologic Clinics. 35 (4): 465–488. doi:10.1016/j.det.2017.06.008. PMID 28886803.
  106. ^ Dubois A, Levecq O, Azimani H, Siret D, Barut A, Suppa M, et al. (October 2018). "Line-field confocal optical coherence tomography for high-resolution noninvasive imaging of skin tumors". Journal of Biomedical Optics. 23 (10): 1–9. Bibcode:2018JBO....23j6007D. doi:10.1117/1.JBO.23.10.106007. PMID 30353716. S2CID 53023955.   This article contains quotations from this source, which is available under the Creative Commons Attribution 3.0 Unported (CC BY 3.0) license.
  107. ^ Velusamy P, Shimada Y, Kanno Z, Ono T, Tagami J (February 2019). "Optical evaluation of enamel white spot lesions around orthodontic brackets using swept-source optical coherence tomography (SS-OCT): An in vitro study". Dental Materials Journal. 38 (1): 22–27. doi:10.4012/dmj.2017-262. PMID 30158348.
  108. ^ Damestani Y, Reynolds CL, Szu J, Hsu MS, Kodera Y, Binder DK, et al. (November 2013). "Transparent nanocrystalline yttria-stabilized-zirconia calvarium prosthesis". Nanomedicine. 9 (8): 1135–1138. doi:10.1016/j.nano.2013.08.002. PMID 23969102. S2CID 14212180.
  109. ^ Mohan G (September 4, 2013). "A window to the brain? It's here, says UC Riverside team". Los Angeles Times.
  110. ^ US patent 7116429, Walecki WJ, Van P, "Determining thickness of slabs of materials", issued 2006-10-03 .
  111. ^ Walecki WJ, Szondy F (2008). Novak EL, Wolfgang O, Gorecki C (eds.). "Integrated quantum efficiency, reflectance, topography and stress metrology for solar cell manufacturing". Proc. SPIE. Interferometry XIV: Applications. 7064: 70640A. Bibcode:2008SPIE.7064E..0AW. doi:10.1117/12.797541. S2CID 120257179.
  112. ^ Walecki WJ, Lai K, Pravdivtsev A, Souchkov V, Van P, Azfar T, Wong T, Lau SH, Koo A (2005). Tanner DM, Ramesham R (eds.). "Low-coherence interferometric absolute distance gauge for study of MEMS structures". Proc. SPIE. Reliability, Packaging, Testing, and Characterization of MEMS/MOEMS IV. 5716: 182. Bibcode:2005SPIE.5716..182W. doi:10.1117/12.590013. S2CID 110785119.
  113. ^ Walecki WJ, Lai K, Souchkov V, Van P, Lau SH, Koo A (2005). "Novel noncontact thickness metrology for backend manufacturing of wide bandgap light emitting devices". Physica Status Solidi C. 2 (3): 984–989. Bibcode:2005PSSCR...2..984W. doi:10.1002/pssc.200460606.
  114. ^ Walecki W, Wei F, Van P, Lai K, Lee T, Lau SH, Koo A (2004). Tanner DM, Rajeshuni R (eds.). "Novel low coherence metrology for nondestructive characterization of high-aspect-ratio microfabricated and micromachined structures". Proc. SPIE. Reliability, Testing, and Characterization of MEMS/MOEMS III. 5343: 55. doi:10.1117/12.530749. S2CID 123249666.
  115. ^ Guss G, Bass I, Hackel R, Demos SG (November 6, 2007). High-resolution 3-D imaging of surface damage sites in fused silica with Optical Coherence Tomography (PDF) (Report). Lawrence Livermore National Laboratory. UCRL-PROC-236270. Archived from the original (PDF) on February 11, 2017. Retrieved December 14, 2010.
  116. ^ Walecki W, Wei F, Van P, Lai K, Lee T, Lau SH, Koo A (2004). Interferometric Metrology for Thin and Ultra-Thin Compound Semiconductor Structures Mounted on Insulating Carriers (PDF). CS Mantech Conference.
  117. ^ a b Zvagelsky, Roman; Mayer, Frederik; Beutel, Dominik; Rockstuhl, Carsten; Gomard, Guillaume; Wegener, Martin (2022-12-12). "Towards in-situ diagnostics of multi-photon 3D laser printing using optical coherence tomography". Light: Advanced Manufacturing. 3 (3): 466–480. doi:10.37188/lam.2022.039. ISSN 2689-9620.
  118. ^ Walecki WJ, Pravdivtsev A, Santos II M, Koo A (August 2006). "High-speed high-accuracy fiber optic low-coherence interferometry for in situ grinding and etching process monitoring". Proc. SPIE. Interferometry XIII: Applications. 6293: 62930D. Bibcode:2006SPIE.6293E..0DW. doi:10.1117/12.675592. S2CID 121209439.
  119. ^ See, for example: "ZebraOptical Optoprofiler: Interferometric Probe".
  120. ^ EP application 2799842, Markl, Daniel; Hannesschläger, Günther & Leitner, Michael et al., "A device and a method for monitoring a property of a coating of a solid dosage form during a coating process forming the coating of the solid dosage form", published 2014-11-05 ; GB application 2513581 ; US application 20140322429 A1 .
  121. ^ Walecki WJ, Szondy F, Wang A (30 April 2009). Xiao H, Fan S (eds.). "Fiber optics low-coherence IR interferometry for defense sensors manufacturing" (PDF). Proc. SPIE. Photonic Microdevices/Microstructures for Sensing. 7322: 73220K. Bibcode:2009SPIE.7322E..0KW. doi:10.1117/12.818381. S2CID 120168355. Archived from the original (PDF) on 20 August 2011. Retrieved 25 May 2011.
  122. ^ Dufour M, Lamouche G, Gauthier B, Padioleau C, Monchalin JP (13 December 2006). "Inspection of hard-to-reach industrial parts using small diameter probes" (PDF). SPIE Newsroom. doi:10.1117/2.1200610.0467. S2CID 120476700. Retrieved December 15, 2010.
  123. ^ Dufour ML, Lamouche G, Detalle V, Gauthier B, Sammut P (April 2005). "Low-Coherence Interferometry, an Advanced Technique for Optical Metrology in Industry". Insight: Non-Destructive Testing and Condition Monitoring. 47 (4): 216–219. CiteSeerX 10.1.1.159.5249. doi:10.1784/insi.47.4.216.63149. ISSN 1354-2575. S2CID 15657288.
  124. ^ Boppart S (11 June 2014). "Developing new optical imaging techniques for clinical use". SPIE Newsroom. doi:10.1117/2.3201406.03.
  125. ^ Al-Azri K, Melita LN, Strange AP, Festy F, Al-Jawad M, Cook R, et al. (March 2016). "Optical coherence tomography use in the diagnosis of enamel defects". Journal of Biomedical Optics. 21 (3): 36004. Bibcode:2016JBO....21c6004A. doi:10.1117/1.jbo.21.3.036004. PMID 26968386.
  126. ^ Iino Y, Ebihara A, Yoshioka T, Kawamura J, Watanabe S, Hanada T, et al. (November 2014). "Detection of a second mesiobuccal canal in maxillary molars by swept-source optical coherence tomography". Journal of Endodontics. 40 (11): 1865–1868. doi:10.1016/j.joen.2014.07.012. PMID 25266471.
  127. ^ Subhash HM, Hogan JN, Leahy MJ (May 2015). "Multiple-reference optical coherence tomography for smartphone applications". SPIE Newsroom. doi:10.1117/2.1201503.005807.
  128. ^ Rank EA, Sentosa R, Harper DJ, Salas M, Gaugutz A, Seyringer D, et al. (January 2021). "Toward optical coherence tomography on a chip: in vivo three-dimensional human retinal imaging using photonic integrated circuit-based arrayed waveguide gratings". Light, Science & Applications. 10 (1): 6. Bibcode:2021LSA....10....6R. doi:10.1038/s41377-020-00450-0. PMC 7785745. PMID 33402664.