19 December 2017 Clinical translation of handheld optical coherence tomography: practical considerations and recent advancements
Author Affiliations +
J. of Biomedical Optics, 22(12), 121715 (2017). doi:10.1117/1.JBO.22.12.121715
Since the inception of optical coherence tomography (OCT), advancements in imaging system design and handheld probes have allowed for numerous advancements in disease diagnostics and characterization of the structural and optical properties of tissue. OCT system developers continue to reduce form factor and cost, while improving imaging performance (speed, resolution, etc.) and flexibility for applicability in a broad range of fields, and nearly every clinical specialty. An extensive array of components to construct customized systems has also become available, with a range of commercial entities that produce high-quality products, from single components to full systems, for clinical and research use. Many advancements in the development of these miniaturized and portable systems can be linked back to a specific challenge in academic research, or a clinical need in medicine or surgery. Handheld OCT systems are discussed and explored for various applications. Handheld systems are discussed in terms of their relative level of portability and form factor, with mention of the supporting technologies and surrounding ecosystem that bolstered their development. Additional insight from our efforts to implement systems in several clinical environments is provided. The trend toward well-designed, efficient, and compact handheld systems paves the way for more widespread adoption of OCT into point-of-care or point-of-procedure applications in both clinical and commercial settings.
Monroy, Won, Spillman, Dsouza, and Boppart: Clinical translation of handheld optical coherence tomography: practical considerations and recent advancements



Advancements in the field of biophotonics, specifically in optical coherence tomography (OCT) imaging, have allowed for numerous discoveries in disease diagnostics and treatment applications in both commercial and clinical applications, driven forward by academic research and development. OCT first provided an optical means to generate noninvasive high-resolution cross-sectional images and depth-resolved measurements of the human eye.12.3 OCT system development today has continued to reduce form factor and cost, while improving on imaging performance (speed, resolution, etc.) and offering more flexibility for applications in a variety of clinical subspecialties beyond ophthalmology.

OCT has followed a similar development trajectory4 as that of other clinically useful medical imaging techniques, albeit at a much more accelerated pace. Ultrasound (US) imaging has an extensive history of development, with its inception sometime around the 1920s, and impactful clinical utility demonstrated in approximately 1958.5 US systems as understood today were first released commercially in cart-based systems around 1980, with improvements in form factor, utility, and capability over time to its present appearance as a compact, well designed, and optimized system for specialized clinical exams.6 Recently, ultracompact, battery powered, and completely self-contained US handheld units have been released that are used in routine checkups, low-resource settings, and emergency situations (EMT type).7 Over a span of 60 years, US became recognized as the gold-standard imaging modality for a wide range of clinically useful diagnostic tests.

In comparison, the rate of development and clinical adoption of OCT has exceeded that pace, given the acceptance of OCT into the ophthalmic community8 as a gold-standard technique for retinal evaluation 20 to 25 years after inception. The adoption of OCT into the clinical pathways of ophthalmology has allowed investigation into numerous pathologies,9,10 and the structure and function of the individual components of the eye, including the cornea,11,12 lens,13,14 iris,15,16 ciliary body,17,18 retina,1920.21.22 microvasculature,23,24 contact lens design and fit,25,26 and even changes in the retina with exposure to space flight.27 It is often more effective to use a desktop- or benchtop-based system for these high-resolution commercial systems, since they usually require more precise optical stability during imaging to provide high-quality images,28 or have complex feedback loops, such as in adaptive optics systems.29,30

Still, there are many use-cases where benchtop systems have been adapted to provide more advantageous and flexible imaging in probe-like units for subjects who do not have sufficient mobility to tolerate a typical eye exam. Examples of these situations range from bedridden patients to life science and animal research subjects, especially when the temperament of the animal or simply its physical size prohibits bringing it to the imaging equipment. The needs of end users have inspired engineers to package full systems into compact, portable carts. These efforts have advanced with the supporting OCT ecosystem31 of vendors, original equipment manufacturers (OEMs), and machine shops.

In this review, the development of handheld OCT systems for applications including and beyond ophthalmology, as well as the supporting technologies and techniques that have helped engineers produce these systems, will be discussed. We also share a more practical overview and perspective of the handheld probe and portable system development from our own group, with specific lessons learned and pitfalls to avoid when developing and using systems use in clinical settings. Next, the overall field of research and development of handheld OCT probes is presented along with a review of the literature, organized by the relative level of system portability, and with specific systems highlighted from most all imaging subspecialties. Finally, next-generation technologies are discussed that will further reduce handheld probe form factor and allow for future handheld integrated systems.


Innovative Engineering and the OCT Ecosystem

The capabilities of the numerous OCT systems that exist today32 allow for broad applicability, ranging from commercial and clinical applications to basic science research. These advancements were able to iterate so quickly, in part, due to the wide commercial availability of hardware, and the development of miniaturized optical components.33 The incredible rate of growth and expansion of OCT34 has greatly benefited from the development trends in other fields, such as the optical telecommunications field, providing improvements in fiber optics, detectors, and light sources. Present day, expertise in design and manufacturing of miniaturized and specialized components, along with the rapid availability of nearly any optical component, allows for various approaches to construct an optical system to fit a specific need. Clinical-quality components from OEM and third party vendors allow researchers to integrate components such as endoscopes and catheters directly and provide a means to produce high-quality and clinically focused research systems.

While the semiconductor industry lends high-performance detection and processing technology that has reduced cost and improved capability, software development also provides improvements in image detection,3536.37 image quality, and signal-to-noise ratio (SNR),3839.40 through techniques such as digital refocusing in interferometric synthetic aperture microscopy,41,42 computational (computer-based) adaptive optics,43 or functional extension techniques such as Doppler and elastography.44 The aforementioned availability of components and hardware, paired with the advances in digital optical design, project management, precision capability at machine shops, and three-dimensional (3-D) printing and computer-aided design (CAD) programs, enables engineers to design and implement a high-quality system.

To aid in later discussion throughout this review, OCT systems can be stratified into different stages, as demonstrated in Fig. 1, by the level of system portability and form factor.

  • Stage 1: Immobile OCT system + fixed sample arm

    These systems occupy significant real estate on an optical (floating) table, typically using a stationary scan stage or mount to image samples. Processing is performed on a large desktop computer and monitor. (Not the focus of this review.)

  • Stage 2: Portable OCT system + tethered handheld probe

    The OCT system, image processing unit, and display are self-contained within a portable cart. An optical breadboard holds and stabilizes optical components in the cart and can be easily reconfigured. The system power supply is not self-contained and requires an external power source (wall outlet). The handheld probe is likely built using mostly off-the-shelf components, but can be packaged into commercial-grade enclosures.

  • Stage 3: Mobile OCT system + handheld probe

    The entire OCT system and tethered handheld probe are completely self-contained (acquisition, processing, display, and rechargeable power source) in a specialized portable cart or system and customized for a single application. Optimizations to reduce weight and form factor may include customized (field-programmable gate array or similar) processing units and imaging hardware. Tradeoffs with scan speed, resolution, or image quality may be more noticeable than in earlier stages at the expense of form factor and cost.

  • Stage 4: Briefcase-sized (or smaller) self-contained handheld OCT system

    A compact, handheld, battery-powered system contains all optical components, processing units, and a display in a form factor no larger or heavier than a small briefcase. The handheld probe hardware and operating software are completely customized for a single application, with basic online processing to ensure reduced power consumption. Robust system packaging meets electrical, liquid, mechanical, and chemical safety specifications for full clinical certification and rigorous daily use.

Fig. 1

Visual representation of stages 1 to 4 OCT systems. As system form factor is reduced, tradeoffs between image quality (SNR, phase stability, resolution, weight, and scan speed) and portability must be managed. For later-stage systems, reducing cost becomes more of a concern as well. Eventually, image quality and system capabilities become more focused on meeting the needs of a clinical application or a commercial product at a specific price point.


Building handheld systems is truly an iterative process, not only for the hardware and software to operate the system but also to define the essential capabilities of a system and how the handheld system is to be used in practice. In recent years, the performance of equipment relative to size and footprint has rapidly improved, reducing the impact of tradeoffs encountered with designing systems. The discussion then often turns to cost and flexibility of hardware and software. However, the motivation to develop a portable system often arises from needs in the research applications work flow. In the next section, we provide insight into this process, how challenges and needs in research projects have shaped the needs for portable systems, and in turn, how these were shaped by the OCT community and ecosystem.


An Iterative Process: Insight in Designing, Building, and Translating Handheld OCT Systems for Clinical Use

A major focus of translational research has been in bringing optical imaging systems and devices out of the lab and into a hospital or clinical setting. Over time, with changing needs from new research projects and specific challenges that arise from the clinical environment, as well as with hardware improvements and availability of components, systems have advanced from lab-based Stage 1 systems to portable Stage 2 systems. Here, some specific clinical applications and practical insight is provided based on experiences in the development and progress toward Stage 2 portable OCT systems.


Intraoperative Assessment of Cancerous Tissue

Breast cancer, the most common cancer women face worldwide (apart from skin cancer) has a projected cost increase for diagnosis and care by at least 30% over the next 3 years.45 However, costs can be significantly reduced through early detection and diagnosis of breast cancer.46 There are numerous procedures available to detect breast cancer, including the physical palpation of breast tissue or noninvasive medical imaging of the breast using mammography (x-ray), US, or magnetic resonance imaging (MRI). After detection, diagnosis is confirmed through the histological analysis of suspicious tissue following biopsy. With a confirmed diagnosis, the extent (stage) of the cancer and the corresponding appropriate treatment options are determined.47 The surgical removal of the tumor is a mainstay treatment option of the disease.48,49

A major problem faced by surgical oncologists when removing cancerous tissue is ensuring that all cancerous tissue is removed, as well as a sufficient buffer, or margin, of potentially reactive tissue around the tumor mass. There is a high rate of re-excision surgeries for breast cancer given the difficulty of appropriately removing the right amount of tissue, especially in breast-conserving surgeries.50 One of the first portable intraoperative OCT systems was contained in a cart aptly named “The Beast” due to its size. The long-term goal for this research and system was to give real-time intraoperative feedback to surgeons by assessing the surgical margin of resected breast lumpectomy specimens. Figure 2 depicts the system, enclosed in a standard medical-grade endoscopy cart, 5  ft tall, with a monitor affixed (hanging) off the top, and a small (<2  ft2) drop shelf that served as the imaging platform. There was a single drawer where tools were kept, along with marking ink that was used to delineate the location of the imaging site for later histological correlations. This OCT system and cart were well received in the operating room, where images were seen in real-time by research, surgical, and nursing staff, many seeing OCT images of surgical margins for the first time. While state-of-the-art for its time, the spectral-domain OCT system was rather rudimentary by today’s standards. To produce cross-sectional and volumetric images, it utilized a scanning stage to translate fresh ex vivo tissue specimens. The system required up to 3 min for image acquisition, depending on the imaged tissue volume, with an axial scan rate of 5 kHz, and axial and transverse resolutions of 8 and 35  μm, respectively. This system, however, provided some of the first intraoperative OCT images from freshly resected tumor masses.51 The system and representative images of negative and positive margins are shown in Fig. 2.

Fig. 2

First-generation intraoperative portable spectral-domain OCT clinical system—“The Beast.” OCT images of ex vivo resected tumor masses provide rapid and label-free discrimination of surgical tumor margins. Intraoperative OCT images were correlated and verified with postoperative histology.51



Assessing Lymph Nodes for Metastatic Disease: System Design and Implementation

While evaluating surgical margins, another major investigational efforts focused on intraoperatively assessing lymph nodes (LN) for the presence of metastatic disease, including micrometastases.52,53 LN resection and postoperative histological analysis is the current standard-of-care54 for clinically staging breast cancer. In practice, surgeons use an injectable dye to visually localize sentinel or axillary LNs, sometimes using preoperative imaging (US, positron-emission tomography) as a guide. Similarly, radioactively labeled tracers, along with a gamma/Geiger counter probe, can be used for intraoperative localization. Locating and removing the sentinel LN(s) allow pathologists to determine whether there has been metastatic progression of cancer. However, this process is notoriously time-consuming and involves postoperative histopathology of thin sections throughout the entire resected LN. The removal of LNs must also be carefully balanced against the risk of lymphedema55 and other long-term complications. Along with other biophotonics researchers, we realized that an intraoperative noninvasive analysis of LNs could provide real-time guidance to surgeons, and in the future, potentially reduce or even prevent unnecessary excision of LNs.

While preliminary investigations into LNs were carried out with “the Beast,” a second-generation cart, shown in Fig. 3, was developed and used for the intraoperative assessment of LNs. This system employed one of the first commercial benchtop OCT systems (Bioptigen) that included a handheld probe. This system and probe contained both a pair of integrated scanning galvanometers for 3-D image acquisition and a visible tracking beam and was retrofitted into a portable cart. Although the system had a handheld probe, it was used primarily in a fixed platform configuration with the probe mounted on a three-axis stage to both translate the probe over large distances across large tissue specimens and reduce motion artifacts. With this system, the assessment of surgical margins and LNs continued and expanded the previous study in scope, sample types, and analysis methods. When compared to the previous system, the improved imaging speed and overall usability of this system significantly increased sample interrogation capabilities within the operating theater. The integrated tracking beam was a key feature that helped ensure that the cross-sectional OCT images could be later correlated with the corresponding histological sections.53 This system also allowed for a simpler preparation protocol before entering into the surgical suite, as there was simply less surface area to wipe down and sterilize. Many of the materials used in this system were also protected against rust, which prevented its appearance and operation from significantly degrading over time.

Fig. 3

Second-generation intraoperative portable spectral-domain OCT clinical system. (a) OCT system schematic and (b) photo of the OCT system. Physical dimensions were greatly reduced over the previous version. (c, e) Representative intraoperative OCT and (d, f) corresponding histopathology images of a normal, nonmetastatic (left) and cancerous metastatic (right) ex vivo human LNs. All scale bars represent 0.5 mm. Modified and reprinted with permission.53



Considerations for In Vivo Imaging: Protocols and System Design

Through these initial intraoperative studies, it was realized that this imaging technology could have its greatest impact by enabling a surgeon to determine if any cancerous tissue was left behind in the in vivo tumor resection bed (tumor cavity) following the removal of the tumor mass. However, achieving this goal would require a completely new system, handheld probe, and imaging protocol to image in situ in a human subject. New procedures were developed and adopted to avoid causing delays due to added research activities in the operating room, including system setup, usage, and imaging protocols that may otherwise unnecessarily increase the time the patient was anesthetized.

Following typical surgical protocols, the OCT imaging procedure involved first passing the handheld probe to the surgical nursing staff to drape the probe in a sterile sheath, and then to the surgeon and into the sterile field to scan the resection bed margin in situ. After scanning, and while the surgeon was working toward completing the surgery and closing the incision, the probe was passed back to the research staff to scan the excised tissue sample outside of the sterile surgical field. If cancer was suspected during either imaging scenario, it was possible to conclude that insufficient tissue was removed. However, because the OCT system, probe, and protocol were not approved for clinical decision making, the collaborating surgeons were not able to act on any intraoperative imaging results. In the near future, it is expected that it will be possible to identify and immediately remove any additional cancerous tissue from the in vivo tumor cavity and resection bed. This project marked one of the first in vivo and in situ intraoperative use of a handheld OCT device inside human subjects.56 The system, probe, and representative data are shown in Fig. 4. This study required many hours of not only technology development and research but also in-depth collaboration with hospital staff to finalize and approve the imaging protocol, and establish the logistics and flow of new procedures in the operating room. For in vivo imaging studies such as these, it is essential to begin a discussion with clinical partners as early as possible, to not only gauge interest but specifically to learn operational norms and restrictions that are present in clinical environments.

Fig. 4

Third-generation intraoperative portable OCT system and handheld probe. (a) System schematic and (b) handheld probe, when used with surgical sheath, can be used intraoperatively and in situ. (c) Handheld probe and OCT system in portable cart. (d) In vivo images from a partial mastectomy margin. (e) Ex vivo confirmation of conjugate side. OCT images were correlated and confirmed with corresponding histology. Reprinted with permission.56


The handheld probe shown in Fig. 4 was acquired through an NIH-supported collaboration with a commercial partner who had acquired FDA approval for the use of their own system. The probe was designed to be completely sealed, tested for electrical discharge, and certified to ensure safe use in human subjects. The probe design and rigorous safety testing greatly accelerated Institutional Review Board (IRB) approval, which otherwise presented a seemingly impassable regulatory hurdle. The cart selected for this intraoperative imaging system was based on those used by automotive technicians, providing storage space, a simple and inoffensive design, and a design suitable for robust daily use in challenging environments. As a required measure of safety, an isolation transformer was added to this system, and all future systems, to prevent any electrical discharge back into the hospital power system, or into our handheld probe or system, to significantly reduce risk to the operator or imaging subject. The transparent, sterile plastic sheath that allowed this probe to be used within the sterile surgical field and placed into a subject’s tumor cavity was vetted against multiple suppliers, as different plastic types often significantly and unpredictably reduced imaging quality. All of these provisions ensured that the standard of care would not be compromised and that the handheld OCT probe met the same sterility standards as other surgical instruments and clinical equipment after being inspected by the hospital Biomedical Engineering Department.

Building a portable imaging system with a handheld probe and fitting it into a small cart is a challenging task. Typically, this requires many iterations of system-wide re-examination to ensure that all components are compatible and design goals are met. One major design parameter was to ensure sufficient airflow in and throughout the cart, given the high-performance computer and optical detection electronics. In an effort to create a cart that could be easily sanitized by the typical wipe-down procedure required before entering into the surgical wing, several vents were initially eliminated on the cart. However, during use and without proper airflow, electronic equipment within the cart would easily overheat and become damaged after a short period of time, first encountered with the video card in the computer. The system was modified to include fan vents to increase airflow and remedy the issue, which was only possible because the sheet metal on the cart was able to accommodate the small loss in structural rigidity.

With this system, it was possible to intraoperatively evaluate surgical breast margins both in situ as well as from resected tissue specimens.56 The previous generation intraoperative systems were transferred for use in studies in veterinary surgical oncology.57 Ongoing intraoperative human imaging studies have expanded to include the construction and use of portable systems for polarization-sensitive OCT for enhanced tumor margin detection58,59 and a portable multiphoton multimodality imaging system for assessing the tumor microenvironment60 in the operating room. Although neither of these next-generation portable systems currently utilizes a handheld probe, this is an active area of technological development.


Optical Imaging in Point-of-Care Settings

In addition to the operating room, other clinical settings exist where real-time point-of-care imaging would be impactful. Primary care is one clinical specialty that is commonly overlooked by device manufacturers, primarily because the operating margins are very slim, and subsequently, only essential equipment can be purchased and utilized.61 However, primary care physicians are on the front line of care, seeing patients before referral to a specialist, and must be knowledgeable about a wide variety of injuries, diseases, infections, and community or societal trends. Physicians often rely on the physical exam and tools that typically only provide a subjective analysis of patient status. While there are significant advancements in laboratory diagnostic tests of blood, fluids, tissues, and in medical imaging, similar advancements have not commensurately followed for primary care. Physicians could more accurately detect and diagnose disease through the use of new tools to provide quantification of many of the conditions they regularly see and qualitatively assess, and more appropriately refer patients to specialists using quantitative evidence-based data.

In the primary care office, precedents of optical imaging instruments exist, including the ophthalmoscope to visualize the retina, and the otoscope to visualize the tympanic membrane (TM, or ear drum). The otoscope, a relatively simple magnifier and illuminator, is routinely used to diagnose otitis media (OM), a common infection of the ear in children. OM causes inflammation of the TM, and the development of an effusion, or fluid buildup within the middle ear, that causes pain and conductive hearing loss.62 Clinicians use the otoscope to visually interrogate the TM and middle ear to qualitatively identify subtle changes to discern infection. Due to the difficulty of accurately assessing the TM, it is challenging for even expert physicians, resulting in a diagnostic accuracy of 70%.63 While other techniques exist to diagnose OM, including tympanometry64 and pneumatic otoscopy,65 they are not regularly used or are difficult to perform correctly.66 Physicians could greatly benefit from a tool that provides specific and quantitative information related to OM. To treat OM, systemic antibiotics may be prescribed, although clinical standards regarding this are in flux.67 Still, OM is one of the most common reasons for a child to visit the primary care office worldwide,68 be prescribed antibiotics,69 and receive surgery under anesthesia.62 Yet, incorrect diagnoses can lead to the inappropriate prescription of antibiotics. This can subsequently lead to increased antibiotic resistance in a large portion of the population, which is a growing concern.70 To address this issue, new low-coherence interferometry (LCI)- and OCT-based handheld probes were developed to better detect, characterize, and quantify OM.

In an initial design, a fiber and fused GRIN lens was added to the inside of a plastic ear speculum tip that attached to a commercial RCA-based video otoscope without modifying any of the internal components. Modifying an existing commercial product to expand functionality also greatly hastened the development of this system. The lens properties were chosen to focus light through the ear canal and onto and through the TM of a human subject. An LCI system that utilized a laptop for control and processing was constructed and placed into a portable cart for use in the otolaryngologist specialist office (Fig. 5). This system provided single A-scans at a rate of 35 kHz through the TM and into any content within the middle ear (effusion and biofilm). This system provided one of the first in vivo optical characterizations of the TM in an animal model72 and in adult human subjects,71 and helped develop a normative library of the depth-resolved scattering characteristics or profiles of various infection states for OM.

Fig. 5

(a) Portable LCI-otoscopy system. (b) Schematic and photograph of the integration of the LCI fiber-based micro-optic probe into an ear speculum tip that would attach to the otoscope head. (c) Schematic and beam profile of the long-working-distance LCI probe, which used a gradient-index (GRIN) lens. Modified and reprinted with permission.71



First-Generation Integrated Handheld Probe for Primary Care

Considering the regular use of both the otoscope and ophthalmoscope in the primary care office, it was realized that it would be possible to expand imaging to include the eye (both anterior and posterior), as well as the skin and oral cavity. A system with this expanded capability could improve upon not only the ophthalmoscope or otoscope but also provide a more comprehensive point-of-care imaging system for all the tissue sites commonly examined in primary care. While the ophthalmoscope can be used for this purpose, it only provides a surface view of the retina, and is difficult to use effectively. With the depth-resolved capabilities of OCT, an integrated system could provide more comprehensive ocular exams, or early screening for diabetic retinopathy (DBR), which slowly causes patients to lose their vision.73 Vision loss occurs through either the leakage of fluid into the macula, which eventually causes macular edema (nonproliferative DBR), or from the growth of new vessels on the retina with resultant scar tissue that restricts vision, and may eventually lead to a detached retina (proliferative DBR). In either case, early detection of these microstructural changes could allow for more immediate preventative action to be taken, mediated through drugs or other more invasive treatments. An expanded system would also potentially allow for examination of common skin diseases and screening for cancers, such as melanoma or basal cell carcinoma (BCC).74 Oral cancer and dental screening could also benefit patients, as oral caries and gingivitis alone pose a large financial burden and are extremely common.75

This portable and multisite primary care imaging system and handheld probe, shown in Fig. 6, enabled optical characterization of these different sites with interchangeable attachments to the probe tip. An interchangeable adapter used a modified cutout that simulated the device head on a commercial otoscope, such that it would be possible to use standard otoscope tips for TM imaging. To observe the skin, oral cavity, or cornea, a metal standoff and eye cup were used, if applicable, which also had the same fitment. To image the retina, an additional adjustable lens and eyecup was developed, along with a flip mirror in the reference arm to have the proper (longer) pathlength. Suitable dispersion compensation to improve image quality was also added. This initial system and probe design lacked a way to visualize the real-time acquired video and OCT scans on the handheld probe, and had the optical patch cable exposed near the grip, both of which increased the difficulty of using the probe. Although the tradeoffs from the combination and implementation of this hardware were apparent during use, this system and handheld probe was the first of its kind.

Fig. 6

Schematic diagram and photograph of the first-generation primary care portable OCT system and handheld scanner. The cart included a broadband source, spectrometer, and additional optical hardware. The handheld scanner contained the sample optical path with galvanometer-based scanning mirrors. With interchangeable tip attachments, the physicians could easily access multiple tissue sites on a patient. Users were able to monitor both video and OCT images of the tissue and save images with a button mounted on the probe handle. Abbreviations: DG, diffraction grating; PC, polarization controller; DC, dispersion compensation materials; NDF, neutral density filter. Modified and reprinted with permission.76


Later, the internal hardware of the handheld probe was redesigned to improve functionality in clinical settings, although the cart remained the same. A microelectromechanical system (MEMS) scanner replaced the pair of galvanometers to reduce the form factor of the handheld probe and provide more stable and adjustable scans. With smaller components, a color charge-coupled device (CCD) camera was also able to be included, although still at a fairly low 480 p resolution, for surface imaging. A 5-in. screen was added to the probe that allowed the user to visualize OCT data and the color surface image in real time. A commercial spectrometer and light source further improved the reliability of this system, which did not require regular maintenance, alignment, or cleaning to maintain performance, especially when moving the system to different clinical sites. This improved system was first used for research in the human eye at a local eye clinic,77,78 and later was used to investigate ear infections in adult subjects.76 Later, the Labview software was refined for a clinical environment, by incorporating larger and more accessible on-screen buttons, clearer display of relevant information, and simplified image and information display of only what was needed when imaging subjects. A separate version of the software was available to test and diagnose problems should they arise and provided information regarding system stability and base function. The improved usability of this system ultimately let the system operator better focus on interacting with the imaging subject. The system was then used at the outpatient otolaryngologist clinic to observe pediatric subjects and catalogued a normative database of different types and stages of ear infections. Notably, inflammatory changes in the TM and middle ear biofilms were regularly identified in human subjects with acute and chronic OM, respectively.79 Some representative images are shown in Fig. 7.

Fig. 7

Redesigned first-generation primary care handheld OCT probe with representative data from pediatric human subjects with normal and infected ears. Left: Handheld unit was upgraded to include a MEMS-based scanning unit, new optics layout, and a small 5-in. LCD screen to display both surface video and cross-sectional OCT images during acquisition. (a–c) Representative cross-sectional OCT images of a normal ear, and ones with acute and chronic ear infections, respectively. (d–f) Representative corresponding digital otoscopy images. Modified and reprinted with permission.79



Second Generation: Design Improvements for Human Subject Imaging

For the second generation of handheld OCT probes for use in primary care settings, one goal was to refine the design of the handheld probe and portable cart for usability. A major consideration during design was in the portability of the system, as different research projects occurred at separate and distant outpatient or specialist clinics. To utilize existing automobile transportation, the height of the cart was limited, although the monitor mount had the ability to lower into the portable cart. Even with a reduced size, it is prudent for a research-based system to maintain access and flexibility for easy access for repair or to realign components, if necessary. Designing the optical layout and form factor of the handheld probe in digital CAD programs allowed for a rapid iterative design process that met design requirements without the need for a costly lens library and mounting equipment for testing. Similarly, through the use of a customized 3-D printed enclosure, the probe form factor was reduced by 30% over the previous iteration by designing only the needed support structures and outer enclosure, moving away from machined bulky metal fixtures. In total, these changes and modifications reduced the weight of the probe to less than 250 g and ensured that the optical alignment was stable through regular daily use and after transport to multiple imaging sites. The visualization screen on the handheld probe was also removed to reduce bulk, and other display and visualization platforms were explored, such as displays strapped to the operator’s forearms. While many integrated display options were available, all we identified were either limiting or did not have the desired appearance. For example, high-quality replacement screens for mobile devices are available to purchase, but driver boards and USB interfaces are rarely available. Other components were too compromised at that time, and had large bezels, or were too heavy to attach onto a handheld device. Finally, all electrical wiring and optical fiber were routed within a protective sheath that also provided some minor strain relief on the cabling, which was a crucial addition to protect the optical fiber from damage during use, storage, or transport. The finalized system and handheld probe are shown in Fig. 8.

Fig. 8

Second-generation primary care system and handheld probe. (a, b) Portable system and handheld probe in the primary care clinic. (c) System in use within our clinical imaging suite. (d) Automated segmentation and thickness analysis of an in vivo human TM. (e) Real-time thickness measurement tracking over time. Modified and reprinted with permission.80,81


During imaging sessions using these handheld probes, it was challenging for pediatric subjects to remain completely still and attentive. Subjects inadvertently moved through the imaging range of the probe, which was only several millimeters, even while sitting relatively still. While images could be stably acquired, motion was often erratic, making the collection of single scans by manipulating the on-screen “stop” and “record” buttons no longer possible, as commonly done in benchtop systems. Similarly, continuously recording all data was too intensive on computer resources. The operating software of this system was redesigned to provide improved saving functionality and file management by implementing a trigger system that allowed the operator to save a buffered queue of previously visualized on-screen images. Operation using this trigger would ensure any data acquired provided useful information for later analysis. Other improvements included an automated thickness measurement algorithm for rapid analysis of the TM,80 shown in Fig. 8, and a Google GLASS headset to visualize data82 since a screen was no longer included on this handheld. This system was later used to evaluate the in vivo viscosity of middle ear effusions, fluid that often accumulates behind the TM in subjects with OM.81 The success achieved in these various projects was in part due to the improved long-term reliability and ease of use of this system, as well as the reduced form factor and weight over the first-generation system. These qualities helped researchers to more efficiently explore various projects in both outpatient and surgical environments.

Additional studies were also conducted to further characterize the anatomical and biomechanical properties of the ear in the presence of OM. The discovery of biofilms adhered to the TM and identified with OCT in a previous study,79 and their continued implication in chronic OM,83 prompted further investigation into the role of biofilms in chronic infections. Biofilms dramatically promote bacterial resistance against antibiotics and immune system activity. Current clinical guidelines for treating OM do not take middle ear biofilms into consideration, as the standard otoscope does not provide any information regarding their presence or absence. The presence of biofilms in chronic OM may explain why tympanostomy tube (TT) placement surgery is most effective at resolving some of the more severe cases of chronic OM.84 TT placement surgery is a standard-of-care treatment85 for chronic OM that inserts a ventilation tube into the eardrum to allow for increased drainage and ventilation of the middle ear cavity, as well as to return normal hearing function. To study and investigate the pathogenesis of OM and the effects of standard-of-care treatment, including the surgical placement of TT, subjects with chronic OM were prospectively and longitudinally observed to assess for the presence or absence of middle-ear biofilms with treatment. This and other studies are currently ongoing to more fully characterize biofilm presence and structure during infection and treatment. If biofilms are shown to be a major driving factor in chronic OM, treatment guidelines may be updated after further study to take the presence of middle ear biofilms into account before prescribing antibiotics.

In later iterations of this handheld probe design, pneumatic capabilities were added, as shown in Fig. 9, that allowed the first demonstration of high-resolution depth-resolved characterization of the TM using fast LCI axial scans with a pneumatic stimulus.86 Subsequently, lower-cost system components were implemented in attempts to reduce the overall cost, both in software87 and hardware.88

Fig. 9

Second-generation primary care imaging handheld probe modified to accommodate pneumatic functionality. (a) A rubber ear-bud tip was added to the ear speculum to ensure a pressure seal within the ear canal, along with a pressure sealed probe tip. (b) System schematic showing an input port for the computer-controlled air pressure stimulus (dotted box). This fast axial-scanning LCI system replaced the two-dimensional (2-D) scanning MEMS-driven mirror to lower costs and capture fast dynamic transients of the TM following the pressure stimulus. Abbreviations: M, gold mirror; C, collimator; DM, dichroic mirror; OBJ, objective.86



Third Generation: Tradeoffs in Complexity, Form Factor, and Cost

For the third generation of primary care systems, the focus centered on further reducing form factor and significantly reducing cost, to where primary care offices could potentially afford a shared system that retained the capabilities of previous generations. Two systems were constructed that utilized different OCT engines and construction materials to reduce cost and weight. Through this design process, powder-coated aluminum carts and side panels were found to be both functional and aesthetically appropriate against transport and daily use, especially when compared to carts created with aluminum frames and plastic panels. Wheel size was an important consideration, mainly to ensure that moving the system could be done smoothly and safely without fear of getting caught on gaps in elevators, or on door jambs, or even simply thick carpet. Larger 4- or 5-in.-diameter medical wheels were found to be optimal for our portable cart designs.

Realizing that repairs and alignment often required access to almost every part of the cart, a CAD program was used to design an esthetically pleasing exterior that could still offer unrestricted access to every component in the cart by removing side panels. The reference arm of the OCT system transitioned to a cage-based system, which greatly reduced the footprint needed to maintain its stability over time. On early handheld probes, commercial otoscope replacement bulbs were used to illuminate a fiber bundle within the probe tip. As technology evolved and became available, a customized light-emitting diode ring and MEMS-collimator alignment package (Advanced MEMS, San Francisco, California) was added to this probe, and thus the form factor was reduced even further.

The overall cost of these systems was considered in relation to the choice of OCT engine and application. Spectral-domain OCT was often the preferred engine to maximize phase stability. New research opportunities utilizing swept-source OCT (SS-OCT) were investigated for imaging deeper into the middle ear cavity. While middle ear biofilms were previously found to be affixed to the TM, the middle ear mucosa was first shown to support biofilm growth.89 Having the capability to detect the presence and extent of biofilms simultaneously on the TM and on the mucosa at a potentially lower cost was a significant benefit. The tradeoffs explored between these two system designs allowed for a better understanding of the range of available commercial equipment at the time, tradeoffs between system design and form factor, and the capability for our intended application versus cost. Studies with these system designs are currently ongoing. When comparing the newer generation to the earlier generations, the portable cart form factor was reduced in size by nearly 40%, and the handheld probe was reduced by 10% to 20%, depending on grip shape. These later systems, shown in Fig. 10, eventually evolved into commercial prototypes.

Fig. 10

Third-generation primary care imaging portable system and handheld probe. (a) CAD schematic of cart layout and interior organization. (b) Portable systems testing different material choices (left: powder-coated metal frame and side panels; right: aluminum frame and plastic panels). (c) Schematic of handheld probe layout and final 3-D-printed enclosure. FM, fold mirror; CO, collimation optics; OBJ, objective lens; DM, dichroic mirror.



Operating Within a Clinical Environment: Resources, Compliance, and Limitations

For many of the studies reviewed here, clinical imaging was performed in partnership with physicians at Carle Foundation Hospital in Urbana, Illinois. When clinical collaborations began in 2000, no dedicated staff or research space was available. However, as research needs grew, dedicated research space with access to the entire hospital through underground tunnels and loading elevators was constructed. This expansion also included research staff to assist in the recruiting and consenting of subjects, as well as assist with IRB compliance. Importantly, this space was used to store equipment, including different portable imaging carts, tools to maintain them, supplies to operate in a clinical environment, and a digital slide scanner to capture images of the corresponding histology. This space serves as an invaluable staging ground between university research labs and the hospital, especially before taking systems into a clinical or surgical environment. Similarly, the assistance from dedicated staff to recruit subjects that closely match recruitment profiles provided an immense operational benefit and were critical in gaining patient and physician trust and confidence in these imaging studies and with prototype research equipment.

One limitation in any clinical environment is the processing and handling of biological tissue, which is typically analyzed, documented, and stored in the pathology department, and cannot be transported offsite. As an initial solution, a relatively inexpensive microscope was built to digitize the histology slides from these clinical studies. These slides were used to correlate intraoperative OCT images against the current gold standard of H&E-stained histopathology. Later, a commercial digital slide scanner was purchased to enable rapid imaging and processing of entire histology slide sets. This system allowed high-resolution digital images of the entire set of histology slides for comparison, ensured that the original slides remained at the hospital, and enabled a more thorough correlation between histology and OCT images.

The use of OCT-needle biopsies was investigated in an attempt to improve breast cancer diagnosis rates and reduce the number of biopsy cores required for small, nonpalpable lesions. While needle biopsies are typically performed as outpatient procedures, it was not possible to develop manufacturing and sterilization procedures that would satisfy IRB and FDA requirements to use lab-built OCT needles and systems in vivo. Instead, OCT needle designs were developed and evaluated in freshly resected ex vivo human tumor masses within the operating room. This helped simulate insertion procedures into real tissue and provided a wealth of information on the structural features of fresh human breast tissue and tumors.90 This approach also provided an opportunity to develop logistics for the construction and handling of OCT needles in a clinical environment. Operationally, it was difficult to precisely correlate the location of the OCT image data with the corresponding histology, as it was often unknown whether a histology section would be analyzed along the same axis or orientation as our needle-based imaging. Similarly, the histological processing of the tissue dramatically changed its shape relative to the precise micron-scale positions of the needle-based measurements with OCT. While this initial study91 was essentially a “fine-needle” biopsy, later studies explored the development and use of “core needle” biopsies. A commercial OCT catheter-based system (LightLab/St. Jude Medical/Abbot Laboratories) was combined with a vacuum-assisted core-needle breast biopsy system (Hologic, Inc.) to enable imaging of both the tissue prior to and immediately after physical biopsy sampling.92 To move to in vivo human imaging and analysis, specialized protocols for sterilization were required for safety and IRB compliance of these modified probes. Other avenues of investigation were pursued.


Design Considerations for Handheld Probes

Ergonomic and user-focused designs are largely missing in many commercial products. A wealth of innovation, however, can be found in industrial design, which can be incorporated early in the development process to explore the usage and human interface between handheld probes and with actual users. Collaborating physicians were observed when using their own typical instruments during procedures, were questioned as to how and why certain tools were used, or held in a specific manner, and where their gaze was fixed during procedures to truly understand the design, intended use, and actual use of the instruments. With this information, the design of various handheld tools, appliances, and instruments used in different fields was then examined to find inspiration for handheld OCT probes. A range of product types and categories were investigated, including children’s toys, consumer healthcare products, hand tools for construction, and even kitchen tools, all of which had excellent ergonomics for their intended use. Representative images from this investigation are shown in Fig. 11. Mood and feel, often difficult to quantify, were also considered, focusing on how an individual interprets any subconscious cues by using, touching, and feeling a tool. The weighting of handheld tools and probes was explored to find a comfortable grip and balance using the same mass and location of optical components used in the handheld probe design, and for users with different hand sizes and anatomy.

Fig. 11

(a) Photos representing different handling techniques of an otoscope during use by an experienced ENT otolaryngologist and (b) different grip shapes, materials, and textures in various commercial products.


Esthetics are also often overlooked in the development and design of portable carts and handheld probes. To facilitate clinical translation and use, systems intended for academic research in clinical environments should look like they belong in a clinical environment. The exterior appearance of the system should reflect the technical development efforts undoubtedly within. This equates to no visible loose wires or fitments, and no visible glue, tape, or other temporary measures for construction. As system designers, engineers are intimately familiar with their systems. Yet, clinical staff and especially imaging subjects are confronted with a completely new situation with a new instrument and new procedures, and carry their own perceptions, doubts, curiosity, and hesitation about any unproven research system or instrument. A unified appearance will help inspire confidence in clinical staff and imaging subjects that the system is safe, well-designed, and robust, and more importantly that it will provide new helpful data during operation. To reinforce this, even the color of portable carts and handheld probes should be modeled after current medical products, if possible.

Working with an industrial design collaborator, nature-inspired designs for future handheld probes were created, with some concept designs shown in Fig. 12. In addition, other interaction and encounter spaces in the patient workflow were explored and redesigned to incorporate next-generation technologies such as OCT systems and handheld probes in primary care. A “Doctor’s office of the future” was designed where lab space was remodeled to support human subject imaging studies, and where human subject volunteers and visitors would feel as if they walked into a real clinical environment. Colors, textures, layout, furniture, and the available equipment in the room were concepts taken into account during the design and renovation of this space. 3-D plastic models and poster diagrams of the human ear, eye, teeth, and skin and a large wall-mounted display helped provide background information to subjects before their exam as well as an opportunity for self-teaching. The large display also allowed imaging results to be efficiently displayed, relayed, and explained to the subject postexamination. In addition, instead of relying on unclear or incorrect online sources, informational websites could be reviewed and explained transparently. This “Shared Care” concept would allow the imaging subject to feel more comfortable and involved in the clinical exam.

Fig. 12

(a) Nature-inspired designs for handheld probes. Many future designs were considered for an ergonomic handheld probe. (b) A “doctor’s office of the future.” This lab space was redesigned for human subject imaging, with special attention given to color, layout, and function. The room not only included standard clinical equipment: otoscope, ophthalmoscope, blood pressure and pulse oximetry measurement systems, and sterile healthcare supplies, but also portable primary care imaging systems and teaching tools.


Finally, no single industry is able to provide the components needed to construct these custom-designed systems, and future system builders are encouraged to explore and creatively use components and parts from many suppliers, ranging from not only suppliers of optics, electronics, and hardware but also medical supply companies, plumbing fixture resellers, and the automobile industry, to name only a few.


Ensuring Stability During Handheld Probe Imaging

Apart from ergonomic and esthetic design choices of a handheld probe, ensuring stability of the subject and optical system during imaging is a challenging task for system designers and operators. The imaging depth of a typical spectral-domain OCT system is several millimeters, which requires accurate positioning of the subject within the focal plane of the handheld probe during image collection. With no external guide, operator and subject instability may prevent the acquisition of useful data. Desktop OCT systems typically employ a floating table, sample rest, and precisely controlled three-axis stage to ensure motion artifacts are minimized during image collection. For benchtop human subject imaging, fixed physical anchors have been effective, such as the ubiquitous chin rest and forehead bar used in retinal imaging.93 Although there are other involuntary ocular movements that occur, this mount reduces neck and body movements that would otherwise make imaging problematic. Similarly, other medical imaging modalities, such as MRI94 and CT,95 restrict subject motion and keep the subject relaxed by laying the subject horizontally, using blankets, and sometimes using restraints or anesthesia. Images can also be collected during periods of brief stability linked to either breathing96 or heart rate,97 as done in other imaging specialties.

While no solution can completely replace a stable system, there are several methods that reduce motion when imaging using handheld probes. Some specialized SS-OCT systems have recently expanded the interrogation depth from several millimeters to several centimeters using new MEMS-vertical-cavity surface-emitting laser technology.98 This helps to provide a wider (deeper) window for image collection, although it does not necessarily improve imaging stability. Some systems, such as buffered FDML systems, simply image at a faster rate,99 which can reduce the interframe movement if the tissue is in focus. Phase stability thresholds for specific applications can also be calculated.100 Most handheld probes are used in contact-mode, employing a precisely crafted standoff to assist the operator at keeping the positioning stable and focused on the tissue site. One common example of this is the ophthalmoscope eye cup that provides the system operator a guide for setting the proper distance from the eye, with finer adjustment done by hand for exact positioning. In some cases, the operator can use their hand and grip to stabilize the probe against the subject, or have the tip standoff anchored around the tissue itself and rely on gentle downward force to prevent movement.

To ensure stable image collection in a system, enabling some adjustability in the imaging range and working distance of the optical system is key. Similarly, a thorough knowledge of typical physiological dimensions and normative bounds of variation among the subject population can also help refine specialized standoff designs. Finally, any buttons or triggers on the probe used to initialize saving data must also be carefully chosen and placed. The trigger pressure, if too high, will cause minor movements that may inadvertently translate the imaging beam around the tissue surface and away from the originally intended interrogation site. Depending on the location of the button relative to the grip, especially if oriented directly along the imaging depth axis, similar translations may move the tissue in and out of the plane of focus.

This section provided a unique retelling of the evolution of intraoperative and primary care imaging systems based on the practical experience and insight from one research group. Many of the technical considerations for system performance, portability, and usability were considered iteratively and simultaneously alongside the operational norms of a clinical environment. Many other groups have also created robust probe and system designs that employ unique technical solutions to solve challenging issues in image acquisition, stability, and beam delivery for many other fields and applications. The next section highlights some of these systems. While many Stage 1 benchtop systems are the backbone of commercial applications of OCT, and other primarily benchtop OCT systems can be used in a handheld configuration with limited functionality, these systems will not be discussed here, as the focus is primarily on handheld OCT systems.


Stage 2 Systems: Biological Discovery Through Technical Innovation

There are a multitude of handheld systems that employ innovative technical solutions to provide a means to observe new biological phenomena. In this section, the varied landscape of Stage 2 handheld systems is surveyed, attempting to capture the breadth of handheld OCT systems and their technical innovations, as well as highlighting the various application subspecialties. While some commercial entities, research startups, and businesses are mentioned here, none are specifically endorsed by the authors of this paper. A thorough review and discussion of commercial OCT efforts is available elsewhere.31,33



Ophthalmology was one of the first research and application areas of OCT, since few other medical imaging modalities provided the needed resolution and noninvasive diagnostic capability to observe the retina and other ocular components. With the recent commercial release of software-based angiography processing in desktop ophthalmic systems, current research interest areas include viewing retinal cells beyond the rods and cones,101 wider fields of view,102 and high-speed imaging.103 Many different systems have been constructed toward achieving one or several of these aims by both research and commercial interests.

One excellent example of the evolution of a handheld design in principle and execution is demonstrated in a combined scanning laser ophthalmoscope (SLO)-OCT handheld retinal system. SLOs are typically used to collect high-speed reflectivity maps of the retina104,105 and when used with fluorescein dyes can visualize vasculature.106 When combined with OCT, a fundus image can be quickly generated along with cross-sectional depth scans.107 Multiple reference designs, CAD drawings, and optical designs have been provided that demonstrate a cohesive effort to produce handheld OCT probes. The original design uses what appears to be a combination of off-the-shelf and custom fabricated aluminum parts to allow for a relatively compact unit.108 A second-generation version109 further reduced the form factor and increased the optical capabilities of the first. As shown in Fig. 13, a third-generation version produced high-resolution images of the retina in a compact handheld,110 shown in pediatric subjects, who are typically more difficult to image than adults. When compared to the first version, its size was reduced by nearly 40× in total volume, yet the probe was still able to produce images of similar quality with a lateral resolution of 7  μm in a model eye, and of sufficient capability to detect the varying densities of parafoveal rods and cone cells in the retina.

Fig. 13

Ultracompact SLO/OCT high-resolution handheld probe with widefield images assembled through mosaicking. (a) Optical design, schematic, and 3-D rendering of ultracompact handheld probe. SLD, superluminescent diode; APD, avalanche photodiode; Sp, spectrometer; BD, beam dump; RA, reference arm; OAP, reflective collimator (off-axes parabolic mirror); L1–L4, lenses. Blue and red text in the schematic corresponds to components used for imaging in the SLO or OCT modes, respectively. (b) Probe in use in a pediatric human subject. (c) SLO image near fovea. (d) Zoom of (c) (dotted red) to parafoveal receptors. (e) Zoom of (d) (dotted teal), with density calculations in several regions across (d). Modified and reprinted with permission.110


Another standout handheld design provided high-speed and widefield observation of the retina in a flexible package.111 This system allowed for efficient screening of retinal pathologies in patients in a clinical environment, given its simplified data collection and fast imaging rate to reduce motion artifiacts. This handheld had an adjustable grip orientation and provided scans of the retina of up to 10×10  mm2 using a 350-kHz A-line rate VCSEL source and photodiode. The handheld screen displayed both a representation of the fundus/iris view and the OCT scan. An optical design schematic illustrates the three optical design paths within the handheld: OCT, iris/fundus camera, and fixation target (Fig. 14).111 Robust handheld systems such as these allow for enhanced screening for ocular trauma or early retinal disease in settings outside of typical clinical environments.

Fig. 14

Handheld MEMS-based OCT probe. Demonstration of different grip styles including (a) “power grip” and (b) “camcorder” styles. (c–e) Optical layouts of (c) OCT 1060 nm optical path, (d) iris camera visible optical path, and (e) fixation target visible optical path. (f–j) Motion-corrected widefield volume; (f) en face OCT fundus image. (g–j) Color-indicated OCT scans from various regions in the retina. Modified and reprinted with permission.111


Angiography is a major focus in clinical imaging of the retina,23,24,112,113 since it provides a view of the vasculature without added dyes or contrast agents. With phase stable OCT data, functional time-resolved changes from blood cells in the microvasculature of the retina can be calculated to create an en face angiogram without the need for any injected contrast or fluorescent dye.23 This is technically difficult to achieve in a handheld, since these techniques are typically limited by the phase stability of the optical system and the optical fiber connected to the handheld probe, as well as the inherent added motion of the user holding the probe and the subject being imaged. One handheld probe has been able to overcome these challenges, notably without the use of mydriatic (dilation) drops, to produce volumetric angiograms of subjects (Fig. 15).114 This system utilized a fast-refocusing tunable lens to quickly lock onto the retina and postacquisition B-scan alignment to correct for motion artifacts from the operator and subject. The sensitivity of the system for imaging capillaries in the retina approaches that of mounted commercial systems and can provide a vessel density map of the retina without the use of any injected contrast agents. This information is useful for clinicians to discern pathological vessel growth in subjects with DBR or other diseases.

Fig. 15

Handheld OCT angiography probe with automated tunable lens focus adjustment. (a) Schematic of the handheld OCTA probe. (b) 3-D perspective view of the probe including all the optical components and the designed plastic case for mounting and holding. (c) Photograph of the handheld OCTA probe with 3-D-printed enclosure. Reprinted with permission.114


Portable and handheld system designs have the capability to bring OCT to atypical situations that require high-resolution imaging and where large benchtop setups are prohibitive. Very often, it is more practical and sometimes necessary to bring the imaging system to the subject, rather than having the subject approach the benchtop imaging system. In one unique case, an elephant was nearly blind and required cataract removal surgery to improve its quality of life. With assistance from a portable OCT system and handheld probe, surgeons were able to remove the cataracts and restore partial vision to this animal,115 although a synthetic lens implantation was not possible given existing damage to ocular tissue. The surgical team is shown with the anesthetized animal in Fig. 16.

Fig. 16

Surgical removal of cataract from C’sar, an African elephant at the North Carolina Zoo. The handheld Envisu R2300 OCT scanner from Bioptigen was used to guide surgeons on this delicate surgery, dramatically improving the quality of life for this patient. Image courtesy of Eric Swanson, OCT News, and Eric Buckland, Leica (Bioptigen).115




There are many target tissue sites that can be observed within the human body via an endoscope, especially when enhanced with OCT.116 Probes with a long distal tip have been used to reach deep into the larynx or the sinuses to allow visualization of these regions. OCT catheters can be directed through the many branches of the cardiovascular system117 or through the gastrointestinal tract,118 and needle-based probes can enable an internal view of solid tissues.119 Ultimately, endoscopic systems allow a user to view tissue within the subject that would otherwise not be possible. These systems rely on their shape or rigidity to navigate the potentially tortuous pathways inside the body, and a rotational or forward scanning mechanism to visualize internal structures of interest. Many of these systems attempt to provide an earlier or improved detection rate of cancer, ameliorate the poor survival rate of some cancers,120 to examine surgical margins,121 assess for the presence of plaques and weakened arterial structure,118 or provide contrast or functionality not available with more traditional techniques, such as Doppler OCT.122

One such example relies on a tethered pill-like capsule that is used as an OCT probe to produce high-resolution images of the esophagus in order to screen for and detect Barrett’s esophagus.123 Initial versions of this system were developed and translated through an iterative process to produce the version currently found in the literature, as shown in Fig. 17. This system was designed for regular clinical use, which took into account the additional considerations and restrictions needed in a clinical environment and to use the device in vivo, such as patient safety and comfort, probe design, and rapid speed of imaging, to name only a few. Many of these aspects are detailed in prior publications.118,124 The tethered capsule design provided a means to access part of the stomach and the entire esophagus with OCT, and this system is now being used in outpatient settings.124 In the future, it may be possible to diagnose pathological esophageal conditions using high-resolution OCT images without the need for biopsy, and do so without the need for specialized healthcare resources or personnel.

Fig. 17

Tethered capsule OCT endomicroscopy. (a) Overview of the device. The tether allows retrieval of the capsule, which also contains the drive shaft and optical fiber, after being swallowed through the esophagus and passing briefly into the stomach of the subject. Inset: schematic of the capsule. (b) Close-up of capsule with scanning mechanism active and positioned adjacent to a US penny for scale. (c) In vivo tethered capsule endomicroscopy image obtained from a patient with histopathologically confirmed Barrett’s esophagus. (d) Threefold (3×) expanded view showing an irregular luminal surface, heterogeneous backscattering, and glands within the mucosa (arrowheads). Tick marks in (c) represent 1 mm. Scale bars represent 0.5 mm. Reprinted with permission from Macmillan Publishers Ltd.123


Rigid endoscopes are also favored when examining the small airway opening or larynx.118,125 One laryngoscope system, shown in Fig. 18, employs a fast and automated focus adjustment unit in the body of the handheld and reference arm, such that the system can interrogate tissue in and around the vocal folds without adjusting the reference arm in the OCT imaging system.126 This is particularly useful to dynamically observe phonating vocal chords, and one excellent example of the handheld probe design ensuring stability during imaging. A swept-source-based OCT system also improves the imaging depth over a spectral-domain-based system.35 In total, this system provides quantitative structural and functional information into mucosal behavior during phonation, expanding the examination capability for other voice disorders.

Fig. 18

Schematic of a handheld rigid laryngoscope-based probe and OCT system. The working distance of the OCT-laryngoscope optical focus can be adjusted by the automated focusing lens, indicated in green, and by the OCT reference arm path-length, indicated in blue. (a) Handheld probe and interrogation area near vocal folds. (b) Photo of handheld probe. Reprinted with permission.126


Needle-based endoscopes or probes allow a view into thick or solid tissue that is typically not possible with traditional imaging systems. There are numerous OCT-based needle probes that allow investigation of the prostate,127 renal tissue,128 deep brain imaging,129 guidance of epidural anesthesia injections,130 breast tissue,90,92 and the examination of the birefringent properties of breast tumors.131 One system enabled the investigation of dynamically moving alveoli in an animal model,132 as shown in Fig. 19.

Fig. 19

Schematic of a handheld OCT needle probe system with a 30-gauge needle. Display shows the 3-D visualization of a fetile lamb lung showing alveoli and bronchiole bifurcations. Length of cylindrical scan is 2 mm. Reprinted with permission.132


Functional OCT imaging provides information about a sample beyond structural morphology, such as in elastography. Elastography of skin and other soft tissue is performed by the modulation of pressure (force) applied to a sample, and based on the dynamic response, the biomechanical properties of the sample can be extracted. Although there are fairly rigid experimental requirements to perform this work, many tissue types have been explored and characterized.133134.135.136 One example is through the use of a commercial probe that was adapted to detect the biomechanical properties of human skin with aging by observing elasticity and scattering metrics, and was performed in vivo on human subjects.137 Still, employing elastography techniques in a handheld probe-based system adds considerable difficulty, as the exact experimental and boundary conditions cannot always be guaranteed. Figure 20 shows one system that provides a method to detect tissue interfaces and was demonstrated in ex vivo tissue.138 A forward-scanning needle probe was used to detect tissue interfaces with this technique.

Fig. 20

Tissue boundary detection using OCT-elastography in a handheld needle probe. (a) Schematic of forward facing needle probe and OCT system. Abbreviations: SLD, superluminescent diode; PC, polarization controller; MTS, motorized translation stage; SMF, single-mode fiber; GRIN, gradient-index fiber. (b) Boundary detection in ex vivo porcine tracheal wall with comparative histology. Scale bar represents 100  μm. Reprinted with permission.138




In cardiology applications, the challenging clinical environment and tortuous access to the human heart places stringent requirements on OCT probes and systems. While research in cardiology began soon after the inception of OCT,139,140 and has continued since,141 intravascular ultrasound (IVUS) still dominates this clinical application. For example, OCT-guided stent placement and IVUS have been shown to have comparable procedure rates despite the improved resolution of OCT.142,143 However, most physicians appreciate the improved image features and resolution that OCT provides, which is 10× the resolution of a standard IVUS image.144 With further research demonstrating, the utility of OCT over IVUS,145 systems demonstrating improved operating speed and ease of use, and especially a reduction in cost, OCT will likely continue to be impactful in cardiology. Most systems used in cardiology applications are catheter based146 and used primarily for the identification of plaques in the coronary arteries,147 evidence of atherosclerosis,148 and for stent placement.147


Dentistry and Dermatology

There are many applications in dentistry where OCT may be useful in the diagnosis of periodontal diseases,149 as well as for oral cancer,150,151 and in observing the effectiveness of various therapies for preventing enamel loss152 or for restoration,153 among many others. One group in particular prepared a highly detailed guide on engineering efforts to design, construct, and test several iterations of a handheld probe for general dental applications,154,155 reviewing design requirements such as material choices and cost. Figure 21 shows the compact and handheld “final prototype” OCT probe developed through this process. Commercial OCT probes for dentistry have been released156 and are beginning to find their way into clinical use.

Fig. 21

Handheld OCT scanner with a one-dimensional galvanometer-based scanner, suitable for small-scale production. (a, b) Exploded view (itemized) and transparent CAD design of the assembly. 1–17: optical components (see citation). (c) Completed handheld probe. Reprinted with permission.154


When applied to the skin, the largest organ in the human body, OCT is often used to screen for melanomas or carcinomas,157,158 or to characterize more common dermatology lesions159 such as rashes, mites/parasites, inflammatory diseases,160 even acne.161 Handheld systems in this specialty need to be able to provide as deep imaging as possible to visualize the full-thickness structures of skin, along with other OCT variants that help to differentiate these conditions, such as Doppler or vascular imaging, to measure the local density of vessels.162 One handheld Gabor-domain OCM probe was able to provide cellular-level resolution in en face OCM images of skin.163 Special scan patterns were developed for this system to provide distortion-free imaging using an MEMS-scanner without postprocessing at 2  μm resolution (axial and lateral). Other commercial systems utilize multibeam and multifocus techniques to achieve a wide field of view and an extended axial imaging range.158,164


Surgical OCT-Enhanced Tools

Many handheld tools have been developed to fulfill a specific functional purpose and provide feedback during delicate surgical procedures.165 Many other surgical tools exist but in a benchtop configuration, depending on clinical needs and workflow. For example, a set of OCT-enhanced surgical microforceps can provide precise depth-positioning for removing thin membranes in retinal surgeries.166 Another vitreoretinal needle-based surgical tool was combined with a miniaturized OCT probe, shown in Fig. 22. The probe utilized a piezoelectric motor to stabilize this vitreoretinal tool in one direction for microsurgery, dampening the natural swaying motions in the hand from 0 to 15 Hz. Dubbed a SMART (smart micromanipulation aided robotic-surgery tool) handheld, stabilization results were verified on a live embryonic animal model. Tools like these will improve a user’s free-hand accuracy when manipulating tissue.

Fig. 22

SMART handheld. (a) CAD design cross section. Abbreviations: FH, front holder; BH, back holder; J, joint; T, tail; ON, outer needle; IN, inner needle; PM, piezoelectric motor; LL, luer-lock combination; OF, optical fiber. (b) Completed probe, compared to a quarter (US currency). Reprinted with permission.167


Another system, shown in Fig. 23, incorporates a compact MEMS-based handheld that can provide Doppler OCT images of vessels to observe successfully reconnected microvascular anastomosis, or the connection of fine vessels and structures during surgery. These and similar systems169 utilize the precise positioning OCT or LCI provides to precisely manipulate tissue in surgical procedures, which will likely improve patient outcomes.

Fig. 23

Intraoperative MEMS-based handheld Doppler OCT probe to observe microvascular anastomosis. (a) CAD design of handheld probe compared to US currency (quarter). (b) Interior optical design within probe. (c) Handheld probe in hand. Reprinted with permission.168



Multimodal Systems: Overcoming Inherent Contrast Limitations in OCT

As discussed briefly, handheld OCT systems have enabled real-time high-resolution cross-sectional imaging from compact units for numerous clinical applications. Despite the ability of OCT to generate images based on the microscopic morphological features of tissue, the contrast in OCT is based largely on the inherent optical scattering properties of the tissue.170 The lack of chemical or molecular specificity brings additional challenges to the interpretation of OCT images, especially when classifying normal and pathological tissues solely based on morphology.171 In addition to contrast limitations, OCT has limited imaging depth due to multiple scattering, and constrained axial or lateral resolution when specialized imaging configurations are not used. To overcome these inherent limitations, many multimodal benchtop systems integrate OCT with another optical imaging modality. Nonlinear and multiphoton microscopy,60,172 fluorescence, Raman spectroscopy (RS), and photoacoustic imaging have been integrated with OCT to leverage the strengths of each modality.32 In this section, recent advances in the development of multimodal handheld probes are highlighted.

RS provides specific biochemical analysis on a single-cell level, based on the optical vibrations from inelastic light scattering phenomena.173 However, its practical feasibility for clinical use is challenging due to the inherently weak Raman scattering and limited spatial information when using power densities that are safe for in vivo use.174 The integration of RS with OCT (RS-OCT) has allowed both morphological and biochemical characterization of the tissue in real-time. Several handheld RS-OCT probes have implemented a common sample arm with independent detection schemes to characterize skin cancer lesions175 and oral tissue.176 A common detector system was also presented for retina and skin imaging177 by incorporating a spectrograph for detection of both OCT and RS signals. Recently, a fiber-based handheld RS-LCI probe, shown in Fig. 24, has been developed.178 The multimodal system was able to differentiate microbial pathogens of infected ear fluid using RS, while LCI provided both depth-resolved microstructure as well as guidance of the RS beam for coregistration. In the future, it may be possible to simultaneously detect a middle ear biofilm and/or fluid, as well as identify the specific strains of bacteria that are present.

Fig. 24

Multimodal handheld probe for sampling ear infections. (a) Schematic setup of the multimodal RS-LCI probe. (b) Schematic of the LCI (top) and RS (bottom) components. (c) Photograph of the fiber-based RS-LCI probe encapsulated into an ear speculum. The inset shows magnified view of both the RS and LCI beam. Abbreviations: SP, spectrometer; LD, laser diode; SLD, superluminescent diode; and MM, multimode. Reprinted with permission.178


Fluorescence imaging (FI) is another optical technique that can be used to generate biomolecular information from tissue. Combined OCT and FI systems have been demonstrated in various imaging probe configurations. Catheter-based probes179,180 have been developed to investigate the cellular microstructure in areas with inflammation caused by atherosclerosis, and similarly in endoscopes, to identify colon cancer.181 One endoscopic system simultaneously delivers and detects OCT and FI signals using a custom dual-clad fiber,182 shown in an all-fiber-optic platform in Fig. 25. By correlating signals from both OCT and fluorescence, a user can simultaneously visualize the vasculature (using FI) and deeper subsurface structures, such as layered tissues and glands (using OCT).

Fig. 25

Combined OCT and FI probe schematic and results. (a) Schematic of distal end of the dual-mode endoscope design. A precision-cut metal enclosure (outer diam.: 2.4 mm) shows struts for minimal beam blockage (<5%). A photograph of the constructed endoscope including the transparent sheath is shown below (outer diam.: 2.9 mm). (b) Representative 2-D cross-sectional OCT image and (c) 3-D volume of ex vivo rabbit esophagus (gray) with the overlaid inner annulus (red) of the fluorescence intensity. The normal layered structures of the esophagus can be clearly visualized, including the epithelium (E), lamina propria (LP), muscularis mucosa (MM), and glands (G). Reprinted with permission.182


Reflectance confocal microscopy (RCM) has also been combined with OCT in a handheld probe, as shown in Fig. 26.183 With this probe, it was possible to obtain volumetric OCT images of BCC, with enhanced cellular-level details at the selected depth of interest using RCM. A custom-made water immersion objective lens with an NA of 0.9 for RCM, and an NA of 0.1 when utilized for OCT, enabled a common path for the handheld probe. Detailed CAD drawings complement the imaging performance of this system, which is able to generate coregistered images of both cross-sectional tissue microstructures as well as en face cellular morphology of BCC in vivo.

Fig. 26

Handheld OCT-RCM probe. (Top) CAD design and schematic. (Bottom) (a) Clinical image of an erythematous macule. (b) Dermoscopy image of shiny white lines and serpentine vessels in the imaging region. (c) En face and (d) cross-sectional OCT images of hypoechoic areas (arrows), suggestive of BCC. (e) RCM showing cord-like structures with peripheral palisading (arrows) admixed with a fibrotic stroma, suggestive of BCC. (f) Histology of the lesion confirms superficial BCC, with multiple small tumor nests originating from the epidermis (H&E, 4×). Modified and reprinted with permission.183


OCT provides greater imaging depth than most other optical imaging modalities, such as confocal microscopy or nonlinear optical imaging. Yet, when compared to nonoptical imaging modalities, such as US imaging, MRI, or x-ray CT, the reduced imaging depth is a limitation in many clinical applications. To circumvent this problem, OCT has been integrated with US for intravascular imaging.184,185 OCT was able to provide enhanced resolution of the vascular microstructures, while US was able to image deeper structures outside of the vessels. Notably, a single miniaturized endoscope capable of OCT, US, and photoacoustic imaging (PAI) has recently been developed for human skin and intravascular imaging,186 illustrated in Fig. 27. A dual-clad fiber was used to deliver light for PAI and OCT, and an integrated ultrasound transducer was used for US and PAI. The inherently coregistered images provide contrast from optical absorption, scattering, and the acoustic properties of tissue, although the imaging speed (15 s per Tri-B-scan) could be improved for more practical clinical in vivo imaging. The coregistered information from multiple modalities with multiple contrast mechanisms and varying penetration depths allows for greater investigation and characterization of disease states in endoscopic applications than a single modality.

Fig. 27

Integrated multimodal (OCT, US, and PAI) probe. (a) Schematic of distal end of probe and optical path. (b) CAD rendering of the probe. (Bottom) Cross-sectional images of human artery with atherosclerotic plaque. (c) PAI image, (d) US image, (e) OCT image, (f) color-coded RGB image, and (g) H & E histology. Reprinted (adapted) with permission from Ref. 186. Copyright (2016) American Chemical Society.



Stage 3 Systems: OCT on the Go

Not all OCT applications occur with access to stable power from a wall outlet. Furthermore, having a portable cart-based system does not guarantee that transit of the system to and from the imaging deployment site will be convenient or feasible for a single person to manage. Similar restrictions exist in factory or commercial quality control (QC) applications, where size and cost are also serious considerations. Food production QC is one area where grains/seeds, meats, and fruits/vegetables are often constantly monitored to identify and track production issues. Recently, the first portable battery-powered OCT system was demonstrated to characterize crop health in the field (Fig. 28).187 The system was designed to be completely self-contained in an 8-kg backpack form that could be easily carried. The battery platform powers everything needed for the OCT system, with a runtime of 6  h.

Fig. 28

Backpack OCT system for crop QC. (a) Schematic of the portable, compact, and battery-powered backpack-OCT system. (b) (1) wearable system, (2) user wearing pack, (3) user scanning plant leaves, and (4) handheld LCD screen. Reprinted with permission.187


The system is unique in that its backpack unit houses all of the optical imaging and detection components, power supply, and computer control. The tethered handheld unit has a small LCD screen and can quickly visualize data for interpretation. The system has also been optimized to save power when not in use. Data are analyzed using a pass/fail classification algorithm that, with further testing in larger studies, could eventually allow the user to identify issues in real-time at the point of measurement, or similarly be used as an automated QC system for food or process manufacturing to identify issues and/or errors.

Engineers designing systems for use in QC188,189 or low-resource settings190191.192.193 have to meet certain requirements for reliable and nearly continuous operation in daily practice. However, in various clinical scenarios194195.196 or military applications in the field,197 users require an even more portable system that can be carried and utilized over a significant period of time in a wider variety of situations and use cases. Systems such as these can be brought to patients, rather than having to bring patients to instruments, which overcomes a significant hurdle that often exists in the delivery of more advanced healthcare.


Stage 4: Future Point-of-Care Devices

Handheld OCT systems have demonstrated comprehensive clinical utility for the early diagnosis of infection and disease. Unfortunately, no fully developed Stage 4 OCT systems (pocket-sized, self-contained) exist to date. Researchers are actively working to reduce the size and cost of OCT systems by considering alternate detection methods198,199 and light sources,200,201 as well as exploring costs and tradeoffs among various OCT platforms. For specific clinical imaging applications, it may be more practical to reduce the performance requirements of the OCT system to save costs and reduce system complexity and size, while still providing the needed data for clinical decision making.

The original configuration for OCT systems was named time-domain OCT (TD-OCT), given its detection scheme. Researchers have continued system development since inception, pushing the limits of these TD-OCT systems.202,203 However, TD-OCT systems have been used less frequently in the last decade because of the improved imaging speed and SNR afforded by Fourier-domain OCT (FD-OCT) systems.35,204 One important advantage of TD-OCT systems, however, is their potential cost advantage over FD-OCT systems, as they do not require expensive spectrometers or fast swept laser sources.

Recently, an integrated handheld LCI system has been developed and demonstrated for in vivo ear imaging,205 based on the principle of linear-OCT.206 The overall cost to develop this system was significantly lower than portable cart-based FD-OCT systems, roughly by a factor of four.81 Other than the light source, all components needed for this initial system design were housed in a 3-D-printed handheld probe, as shown in Fig. 29. The measured axial resolution and sensitivity of the system were around 5.2  μm and 80 dB, respectively.

Fig. 29

Reduced cost linear-OCT handheld probe for ear imaging. (a) Optical layout of handheld probe. (b) An averaged A-line from a TM recorded from an in vivo human subject. (c) Completed (cover removed) handheld LCI imaging probe. Abbreviations: SLD, superluminescent diode; COL, collimation optics; BS1/BS2, 50:50 beam splitter; OBJ, objective lens; DM, dichroic mirror; DC, dispersion compensation; TS, translation stage; C1/C2, 2-D CCD camera for recording interference and surface images. Reprinted with permission.205


Multiple reference OCT (MROCT) systems are another low-cost TD-OCT technology, based on the optical system within a CD/DVD computer drive. This platform has the potential to enable a wide range of point-of-care and personal care applications.207 In MROCT, a depth scan is achieved by utilizing a partial mirror and actuator to generate a recirculating optical delay line, which extends the axial scan range. The overall cost and size of a typical MROCT system is anticipated to be similar to a CD/DVD unit, although these units are still in the early stages of development.208

Given the advantages of Fourier-based systems over TD-OCT, miniaturizing an FD-OCT system has great potential to be useful in clinical applications, especially in low-resource settings. Instead of utilizing standard spectrometers and CCD cameras, systems developed on a miniaturized silicon-based photonics platform can ideally utilize the cost-savings from mass production capabilities in the semiconductor industry. Recently, a commercial entity created an OCT system that retails for less than $10,000 USD.209 Although limited information is currently available on its design, this achievement was possible given the use of components manufactured at scale for other industries, paired with cost-reduction in other key OCT components such as a reflective parabolic mirror to collimate the light, a liquid lens to scan the beam over a sample, a “loop design” spectrometer, and a low-cost line-scan array detector used for scanning and reading bar-codes.

One research group created an integrated silicon-based arrayed-waveguide spectrometer,210 although it still required an external line-scan camera. Later, a “TriPleX” interferometer platform for SS-OCT was fabricated on a chip platform, which integrates a Michelson interferometer, sample and reference arms, and ports for external balanced photodiode detectors.211 Soon after, these two systems were combined to provide a combined high-quality silicon-based FD-OCT interferometer and spectrometer unit,212 which provided high-quality images of in vivo human skin with an SNR of 74 dB. Another system for SS-OCT integrated the complete dual-balanced quadrature detection system on a chip,213 with a detection sensitivity of 94 dB.

Often, these systems are unexpectedly limited by their compact size, as useful working distances for biomedical applications frequently require an external reference arm to properly match optical delay. To overcome this issue, one system added an on-chip long-path reference arm for SD-OCT systems,214 and later incorporated grating couplers to be compatible with SS-OCT systems.215 In both designs, the light source and spectrometer or detectors were separate from the integrated optical paths and interferometer. There are now efforts to fully integrate all of these components into a single integrated platform. Recently, an integrated platform for SS-OCT combined a significant amount of detector and interferometer components onto a single platform,216 although an external laser system was still required. Systems such as these aim to have a design that encourages a silicon-based fabrication process that can be scaled to commercial levels and significantly reduce the unit cost.

With the continual size reduction and improvement of these silicon-based OCT chips, as well as the expanding OCT ecosystem, it is feasible that an entire OCT system could one day be miniaturized into a fully contained battery-powered handheld package. Situations that will benefit enormously from this technical development of miniaturized OCT systems are users and subjects in remote areas where a decentralized, tiered, and distributed healthcare system exists, or in emergency situations where a quick observational tool could rapidly determine care in a time-critical environment. Similarly, cost-effective access to OCT imaging technology can only benefit future adopters of this technology, for any application.



In conclusion, only a subset of the many advances in handheld OCT technology that have evolved since the inception of OCT in the early 1990s have been discussed here. The new level of refinement of commercial systems, and even research systems, is a testament to the hard work and dedication of OCT researchers and engineers, as well as the many clinical partners who have driven the biomedical imaging applications of OCT. The availability of optical and hardware components from the commercial OCT ecosystem has also enabled advances out of laboratories that were once limited to design engineering firms. As OCT handheld probes continue to develop and mature, we expect the technology will find an even broader user base and serve as an indispensable tool for high-resolution, noninvasive, and nondestructive imaging.


S.A. Boppart is a cofounder and chief medical officer of PhotoniCare, Inc., which is developing optical imaging systems for the ear, and Diagnostic Photonics, Inc., which is developing optical imaging systems for cancer detection. S.A.B. also discloses intellectual property owned by the Massachusetts Institute of Technology and the University of Illinois at Urbana-Champaign related to OCT, and licensed to commercial entities, related to the technology and analysis methods described in parts of this manuscript. Other authors report no disclosures or conflicts of interest.


We would like to thank the many colleagues, researchers, and physicians who have helped develop and establish OCT as an optical imaging platform. While we have attempted to capture the breadth of the handheld OCT technology and its applications, we regret that space limits constrain this review from being more comprehensive. We would like to thank Prof. Deana McDonaugh and Janus Yuan from the School of Art + Design at the University of Illinois at Urbana-Champaign for their design expertise and assistance in visioning and designing user-focused handheld probes and the clinical imaging suite at the Beckman Institute for Advanced Science and Technology. The research presented here from the Biophotonics Imaging Laboratory and the writing of this review was supported in part by the National Institutes of Health (R01 EB013723 and R01 CA213149). Additional information can be found at  http://biophotonics.illinois.edu.


1. A. F. Fercher, K. Mengedoht and W. Werner, “Eye-length measurement by interferometry with partially coherent light,” Opt. Lett. 13(3), 186–188 (1988).OPLEDP0146-9592 http://dx.doi.org/10.1364/OL.13.000186 Google Scholar

2. D. Huang et al., “Optical coherence tomography,” Science 254(5035), 1178–1181 (1991).SCIEAS0036-8075 http://dx.doi.org/10.1126/science.1957169 Google Scholar

3. E. A. Swanson et al., “In vivo retinal imaging by optical coherence tomography,” Opt. Lett. 18(21), 1864–1866 (1993).OPLEDP0146-9592 http://dx.doi.org/10.1364/OL.18.001864 Google Scholar

4. M. L. Gabriele et al., “Optical coherence tomography: history, current status, and laboratory work,” Invest. Ophthalmol. Visual Sci. 52(5), 2425–2436 (2011). http://dx.doi.org/10.1167/iovs.10-6312 Google Scholar

5. I. Donald, J. Macvicar and T. G. Brown, “Investigation of abdominal masses by pulsed ultrasound,” Lancet 271(7032), 1188–1195 (1958).LANCAO0140-6736 http://dx.doi.org/10.1016/S0140-6736(58)91905-6 Google Scholar

6. A. L. Klibanov and J. A. Hossack, “Ultrasound in radiology: from anatomic, functional, molecular imaging to drug delivery and image-guided therapy,” Invest. Radiol. 50(9), 657–670 (2015). http://dx.doi.org/10.1097/RLI.0000000000000188 Google Scholar

7. M. J. Liebo et al., “Is pocket mobile echocardiography the next-generation stethoscope? A cross-sectional comparison of rapidly acquired images with standard transthoracic echocardiography,” Ann. Intern. Med. 155(1), 33–38 (2011).AIMEAS0003-4819 http://dx.doi.org/10.7326/0003-4819-155-1-201107050-00005 Google Scholar

8. M. Kaschke et al., “Optical coherence tomography,” Opt. Photonik 4(4), 24–28 (2009). http://dx.doi.org/10.1002/opph.v4.4 Google Scholar

9. P. A. Keane and S. R. Sadda, “Retinal imaging in the twenty-first century: state of the art and future directions,” Ophthalmology 121(12), 2489–2500 (2014).OPANEW0743-751X http://dx.doi.org/10.1016/j.ophtha.2014.07.054 Google Scholar

10. R. K. Murthy et al., “Clinical applications of spectral domain optical coherence tomography in retinal diseases,” Biomed. J. 39(2), 107–120 (2016). http://dx.doi.org/10.1016/j.bj.2016.04.003 Google Scholar

11. M. Ang et al., “Evaluation of a micro-optical coherence tomography for the corneal endothelium in an animal model,” Sci. Rep. 6(1), 29769 (2016). http://dx.doi.org/10.1038/srep29769 Google Scholar

12. R. M. Werkmeister et al., “Ultrahigh-resolution OCT imaging of the human cornea,” Biomed. Opt. Express 8(2), 1221–1239 (2017).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.8.001221 Google Scholar

13. S. R. Uhlhorn et al., “Refractive index measurement of the isolated crystalline lens using optical coherence tomography,” Vision Res. 48(27), 2732–2738 (2008).VISRAM0042-6989 http://dx.doi.org/10.1016/j.visres.2008.09.010 Google Scholar

14. S. Ortiz et al., “In vivo human crystalline lens topography,” Biomed. Opt. Express 3(10), 2471–2488 (2012).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.3.002471 Google Scholar

15. B. Basarir et al., “Analysis of iris structure and iridocorneal angle parameters with anterior segment optical coherence tomography in Fuchs’ uveitis syndrome,” Int. Ophthalmol. 33(3), 245–250 (2013).INOPDR0165-5701 http://dx.doi.org/10.1007/s10792-012-9680-8 Google Scholar

16. A. Invernizzi et al., “Three-dimensional morphometric analysis of the iris by swept-source anterior segment optical coherence tomography in a Caucasian population,” Invest. Ophthalmol. Visual Sci. 56(8), 4796–4801 (2015). http://dx.doi.org/10.1167/iovs.15-16483 Google Scholar

17. Y. Shao et al., “Simultaneous real-time imaging of the ocular anterior segment including the ciliary muscle during accommodation,” Biomed. Opt. Express 4(3), 466–480 (2013).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.4.000466 Google Scholar

18. S. C. Hau et al., “Evaluation of iris and iridociliary body lesions with anterior segment optical coherence tomography versus ultrasound B-scan,” Br. J. Ophthalmol. 99(1), 81–86 (2014).BJOPAL0007-1161 http://dx.doi.org/10.1136/bjophthalmol-2014-305218 Google Scholar

19. L. M. Sakata et al., “Optical coherence tomography of the retina and optic nerve: a review,” Clin. Exp. Ophthalmol. 37(1), 90–99 (2009). http://dx.doi.org/10.1111/ceo.2009.37.issue-1 Google Scholar

20. M. Adhi and J. S. Duker, “Optical coherence tomography–current and future applications,” Curr. Opin. Ophthalmol. 24(3), 213–221 (2013). http://dx.doi.org/10.1097/ICU.0b013e32835f8bf8 Google Scholar

21. R. J. Zawadzki et al., “Adaptive-optics SLO imaging combined with widefield OCT and SLO enables precise 3D localization of fluorescent cells in the mouse retina,” Biomed. Opt. Express 6(6), 2191–2210 (2015).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.6.002191 Google Scholar

22. R. S. Jonnal et al., “A review of adaptive optics optical coherence tomography: technical advances, scientific applications, and the future,” Invest. Ophthalmol. Visual Sci. 57(9), OCT51–OCT68 (2016). http://dx.doi.org/10.1167/iovs.16-19103 Google Scholar

23. T. E. de Carlo et al., “A review of optical coherence tomography angiography (OCTA),” Int. J. Retina Vitreous 1(5), 1–15 (2015). http://dx.doi.org/10.1186/s40942-015-0005-8 Google Scholar

24. S. S. Gao et al., “Optical coherence tomography angiography,” Invest. Ophthalmol. Visual Sci. 57(9), OCT27–OCT 36 (2016). http://dx.doi.org/10.1167/iovs.15-19043 Google Scholar

25. B. R. Davidson and J. K. Barton, “Application of optical coherence tomography to automated contact lens metrology,” J. Biomed. Opt. 15(1), 016009 (2010).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.3292598 Google Scholar

26. X. Liu et al., “Effect of contact lens on optical coherence tomography imaging of rodent retina,” Curr. Eye Res. 38(12), 1235–1240 (2013).CEYRDM0271-3683 http://dx.doi.org/10.3109/02713683.2013.815218 Google Scholar

27. T. H. Mader et al., “Optic disc edema, globe flattening, choroidal folds, and hyperopic shifts observed in astronauts after long-duration space flight,” Ophthalmology 118(10), 2058–2069 (2011).OPANEW0743-751X http://dx.doi.org/10.1016/j.ophtha.2011.06.021 Google Scholar

28. N. D. Shemonski et al., “Computational high-resolution optical imaging of the living human retina,” Nat. Photonics 9(7), 440–443 (2015).NPAHBY1749-4885 http://dx.doi.org/10.1038/nphoton.2015.102 Google Scholar

29. O. P. Kocaoglu et al., “Adaptive optics optical coherence tomography at 1 MHz,” Biomed. Opt. Express 5(12), 4186–4200 (2014).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.5.004186 Google Scholar

30. K. Kurokawa, Z. Liu and D. T. Miller, “Adaptive optics optical coherence tomography angiography for morphometric analysis of choriocapillaris,” Biomed. Opt. Express 8(3), 1803–1822 (2017).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.8.001803 Google Scholar

31. E. A. Swanson and J. G. Fujimoto, “The ecosystem that powered the translation of OCT from fundamental research to clinical and commercial impact,” Biomed. Opt. Express 8(3), 1638–1664 (2017).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.8.001638 Google Scholar

32. W. Drexler et al., “Optical coherence tomography today: speed, contrast, and multimodality,” J. Biomed. Opt. 19(7), 071412 (2014).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.JBO.19.7.071412 Google Scholar

33. J. Fujimoto and E. Swanson, “The development, commercialization, and impact of optical coherence tomography–history of optical coherence tomography,” Invest. Ophthalmol. Visual Sci. 57(9), OCT1–OCT13 (2016). http://dx.doi.org/10.1167/iovs.16-19963 Google Scholar

34. E. A. Swanson, “Estimates of ophthalmic OCT market size and the dramatic reduction in reimbursement payments,” OCT News, 2012,  http://www.octnews.org/articles/4176266/estimates-of-ophthalmic-oct-market-size-and-the-dr/ (June 2017). Google Scholar

35. M. A. Choma et al., “Sensitivity advantage of swept source and Fourier domain optical coherence tomography,” Opt. Express 11(18), 2183–2189 (2003).OPEXFF1094-4087 http://dx.doi.org/10.1364/OE.11.002183 Google Scholar

36. D. L. Marks et al., “Digital algorithm for dispersion correction in optical coherence tomography for homogeneous and stratified media,” Appl. Opt. 42(2), 204–217 (2003).APOPAI0003-6935 http://dx.doi.org/10.1364/AO.42.000204 Google Scholar

37. J. A. Izatt, M. A. Choma, “Theory of optical coherence tomography,” in Optical Coherence Tomography, , W. Drexler and J. G. Fujimoto, Eds., pp. 47–72, Springer, Berlin, Heidelberg (2008). Google Scholar

38. Y. Du et al., “Speckle reduction in optical coherence tomography images based on wave atoms,” J. Biomed. Opt. 19(5), 056009 (2014).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.JBO.19.5.056009 Google Scholar

39. A. Curatolo et al., “Quantifying the influence of Bessel beams on image quality in optical coherence tomography,” Sci. Rep. 6(1), 23483 (2016). http://dx.doi.org/10.1038/srep23483 Google Scholar

40. S. Adabi et al., “Optical coherence tomography technology and quality improvement methods for optical coherence tomography images of skin: a short review,” Biomed. Eng. Comput. Biol. 8(1), 1–5 (2017). http://dx.doi.org/10.1177/1179597217713475 Google Scholar

41. T. S. Ralston et al., “Inverse scattering for optical coherence tomography,” J. Opt. Soc. Am. A 23(5), 1027–1037 (2006).JOAOD60740-3232 http://dx.doi.org/10.1364/JOSAA.23.001027 Google Scholar

42. T. S. Ralston et al., “Interferometric synthetic aperture microscopy,” Nat. Phys. 3(1), 129–134 (2007).NPAHAX1745-2473 http://dx.doi.org/10.1038/nphys514 Google Scholar

43. Y.-Z. Liu et al., “Computational optical coherence tomography,” Biomed. Opt. Express 8(3), 1549–1574 (2017).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.8.001549 Google Scholar

44. J. Kim et al., “Functional optical coherence tomography: principles and progress,” Phys. Med. Biol. 60(10), R211–R237 (2015). http://dx.doi.org/10.1088/0031-9155/60/10/R211 Google Scholar

45. N. Howlader et al., “SEER cancer statistics review 1975–2014,” National Cancer Institute, Bethesda, Maryland,  https://seer.cancer.gov/csr/1975_2014/ (November 2017). Google Scholar

46. H. Blumen, K. Fitch and V. Polkus, “Comparison of treatment costs for breast cancer, by tumor stage and type of service,” Am. Health Drug Benefits 9(1), 23–32 (2016). Google Scholar

47. PDQ, “Adult treatment editorial board. Breast cancer treatment: health professional version,” in PDQ Cancer Information Summaries, National Cancer Institute, Bethesda, Maryland,  https://www.ncbi.nlm.nih.gov/books/NBK65744/ (November 2017). Google Scholar

48. M. S. Moran et al., “Society of Surgical Oncology–American Society for Radiation Oncology–consensus guideline on margins for breast-conserving surgery with whole-breast irradiation in stages I and II invasive breast cancer,” J. Clin. Oncol. 32(14), 1507–1515 (2014).JCONDN0732-183X http://dx.doi.org/10.1200/JCO.2013.53.3935 Google Scholar

49. M. Morrow et al., “Society of Surgical Oncology-American Society for Radiation Oncology–consensus guideline on margins for breast-conserving surgery with whole-breast irradiation in ductal carcinoma in situ,” J. Clin. Oncol. 34(33), 4040–4046 (2016).JCONDN0732-183X http://dx.doi.org/10.1200/JCO.2016.68.3573 Google Scholar

50. M. Dieterich et al., “Re-excision rates and local recurrence in breast cancer patients undergoing breast conserving therapy,” Obstet. Gynecol. 72(11), 1018–1023 (2012).OBGNAS0029-7844 http://dx.doi.org/10.1055/s-0032-1327980 Google Scholar

51. F. T. Nguyen et al., “Optical coherence tomography: the intraoperative assessment of lymph nodes in breast cancer,” IEEE Eng. Med. Biol. 29(2), 63–70 (2010).IEMBDE0739-5175 http://dx.doi.org/10.1109/MEMB.2009.935722 Google Scholar

52. S. A. Boppart et al., “Optical coherence tomography: feasibility for basic research and image-guided surgery of breast cancer,” Breast Cancer Res. Treat. 84(1), 85–97 (2004).BCTRD6 http://dx.doi.org/10.1023/B:BREA.0000018401.13609.54 Google Scholar

53. R. M. Nolan et al., “Intraoperative optical coherence tomography for assessing human lymph nodes for metastatic cancer,” BMC Cancer 16(1), 1–10 (2016).BCMACL1471-2407 http://dx.doi.org/10.1186/s12885-016-2194-4 Google Scholar

54. A. Chatterjee, N. Serniak and B. J. Czerniecki, “Sentinel lymph node biopsy in breast cancer: a work in progress,” Cancer J. 21(1), 7–10 (2015). http://dx.doi.org/10.1097/PPO.0000000000000090 Google Scholar

55. S. A. Norman et al., “Lymphedema in breast cancer survivors: incidence, degree, time course, treatment, and symptoms,” J. Clin. Oncol. 27(3), 390–397 (2009).JCONDN0732-183X http://dx.doi.org/10.1200/JCO.2008.17.9291 Google Scholar

56. S. J. Erickson-Bhatt et al., “Real-time imaging of the resection bed using a handheld probe to reduce incidence of microscopic positive margins in cancer surgery,” Cancer Res. 75(18), 3706–3712 (2015).CNREA80008-5472 http://dx.doi.org/10.1158/0008-5472.CAN-15-0464 Google Scholar

57. K. J. Mesa et al., “Intraoperative optical coherence tomography for soft tissue sarcoma differentiation and margin identification,” Lasers Surg. Med. 49(3), 240–248 (2017).LSMEDI0196-8092 http://dx.doi.org/10.1002/lsm.22633 Google Scholar

58. F. A. South et al., “Differentiation of ex vivo human breast tissue using polarization-sensitive optical coherence tomography,” Biomed. Opt. Express 5(10), 3417–3426 (2014).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.5.003417 Google Scholar

59. F. A. South et al., “Polarization-sensitive interferometric synthetic aperture microscopy,” Appl. Phys. Lett. 107(21), 211106 (2015).APPLAB0003-6951 http://dx.doi.org/10.1063/1.4936236 Google Scholar

60. H. Tu et al., “Stain-free histopathology by programmable supercontinuum pulses,” Nat. Photonics 10(8), 534–540 (2016).NPAHBY1749-4885 http://dx.doi.org/10.1038/nphoton.2016.94 Google Scholar

61. D. R. Willis, “How to decide whether to buy new medical equipment,” Fam. Pract. Manage. 11(3), 53–58 (2004). Google Scholar

62. A. G. Schilder et al., “Otitis media,” Nat. Rev.: Dis. Primers 2(1), 16063 (2016). http://dx.doi.org/10.1038/nrdp.2016.63 Google Scholar

63. R. Linsk et al., Otitis Media Guideline for Clinical Care, 2007, University of Michigan Health System, Ann Arbor, Michigan (May 2015). Google Scholar

64. K. K. Helenius et al., “Tympanometry in discrimination of otoscopic diagnoses in young ambulatory children,” Pediatr. Infect. Dis. J. 31(10), 1003–1006 (2012). http://dx.doi.org/10.1097/INF.0b013e31825cac94 Google Scholar

65. W. S. Jones and P. H. Kaleida, “How helpful is pneumatic otoscopy in improving diagnostic accuracy?” Pediatrics 112(3), 510–513 (2003).PEDIAU0031-4005 http://dx.doi.org/10.1542/peds.112.3.510 Google Scholar

66. E. Morris et al., “Development and validation of a novel ear simulator to teach pneumatic otoscopy,” Simul. Healthcare 7(1), 22–26 (2012). http://dx.doi.org/10.1097/SIH.0b013e31822eac39 Google Scholar

67. R. M. Rosenfeld et al., “Clinical practice guideline: otitis media with effusion (update),” Otolaryngol.–Head Neck Surg. 154(1 Suppl.), S1–S41 (2016).OTOLDL0161-6439 http://dx.doi.org/10.1177/0194599815623467 Google Scholar

68. A. Qureishi et al., “Update on otitis media: prevention and treatment,” Infect. Drug Resist. 7(1), 15–24 (2014). http://dx.doi.org/10.2147/IDR.S39637 Google Scholar

69. R. Yang et al., “Treatment of otitis media by transtympanic delivery of antibiotics,” Sci. Transl. Med. 8(356), 356ra120 (2016). http://dx.doi.org/10.1126/scitranslmed.aaf4363 Google Scholar

70. J. S. Gerber et al., “Effect of an outpatient antimicrobial stewardship intervention on broad-spectrum antibiotic prescribing by primary care pediatricians: a randomized trial,” J. Am. Med. Assoc. 309(22), 2345–2352 (2013).JAMAAP0098-7484 http://dx.doi.org/10.1001/jama.2013.6287 Google Scholar

71. C. T. Nguyen et al., “Noninvasive in vivo optical detection of biofilm in the human middle ear,” Proc. Natl. Acad. Sci. U. S. A. 109(24), 9529–9534 (2012). http://dx.doi.org/10.1073/pnas.1201592109 Google Scholar

72. C. T. Nguyen et al., “Non-invasive optical interferometry for the assessment of biofilm growth in the middle ear,” Biomed. Opt. Express 1(4), 1104–1116 (2010).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.1.001104 Google Scholar

73. “Diabetic retinopathy PPP–updated 2016,” in American Academy of Ophtalmology—Preferred Practice Guideline Retina / Vitreous Panel, Hoskins Center for Quality Eye Care, San Francisco, California (2016). Google Scholar

74. G. P. Guy et al., “Vital signs: melanoma incidence and mortality trends and projections–United States, 1982–2030,” Morb. Mortal. Wkly. Rep. 64(21), 591–596 (2015). Google Scholar

75. R. Rychlik et al., “A global approach to assess the economic benefits of increased consumption of sugar-free chewing gum,” Am. J. Dent. 30(2), 77–83 (2017).AJDEES Google Scholar

76. W. Jung et al., “Handheld optical coherence tomography scanner for primary care diagnostics,” IEEE Trans. Biomed. Eng. 58(3), 741–744 (2011).IEBEAX0018-9294 http://dx.doi.org/10.1109/TBME.2010.2096816 Google Scholar

77. R. L. Shelton et al., “Optical coherence tomography for advanced screening in the primary care office,” J. Biophotonics 7(7), 525–533 (2014). http://dx.doi.org/10.1002/jbio.201200243 Google Scholar

78. S. I. Sayegh et al., “Comparison of a MEMS-based handheld OCT scanner with a commercial desktop OCT system for retinal evaluation,” Transl. Vision Sci. Technol. 3(3), 1–9 (2014). http://dx.doi.org/10.1167/tvst.3.3.1 Google Scholar

79. G. L. Monroy et al., “Noninvasive depth-resolved optical measurements of the tympanic membrane and middle ear for differentiating otitis media,” Laryngoscope 125(8), E276–E282 (2015).LARYA80023-852X http://dx.doi.org/10.1002/lary.v125.8 Google Scholar

80. Z. Hubler et al., “Real-time automated thickness measurement of the in vivo human tympanic membrane using optical coherence tomography,” Quant. Imaging Med. Surg. 5(1), 69–77 (2015). http://dx.doi.org/10.3978/j.issn.2223-4292.2014.11.32 Google Scholar

81. G. L. Monroy et al., “Non-invasive optical assessment of viscosity of middle ear effusions in otitis media,” J. Biophotonics 10(3), 394–403 (2017). http://dx.doi.org/10.1002/jbio.201500313 Google Scholar

82. G. L. Monroy et al., “Implementation and evaluation of Google GLASS for visualizing real-time image and patient data in the primary care office,” Proc. SPIE 8935, 893514 (2014). http://dx.doi.org/10.1117/12.2040221 Google Scholar

83. R. G. Jensen et al., “Recurrent otorrhea in chronic suppurative otitis media: is biofilm the missing link?” Eur. Arch. Oto-Rhino-Laryngol. 274(7), 2741–2747 (2017).EAOTE7 http://dx.doi.org/10.1007/s00405-017-4586-8 Google Scholar

84. J. M. Coticchia et al., “New paradigms in the pathogenesis of otitis media in children,” Front. Pediatr. 1(1), 52 (2013). http://dx.doi.org/10.3389/fped.2013.00052 Google Scholar

85. I. F. Wallace et al., “Surgical treatments for otitis media with effusion: a systematic review,” Pediatrics 133(2), 296–311 (2014).PEDIAU0031-4005 http://dx.doi.org/10.1542/peds.2013-3228 Google Scholar

86. R. L. Shelton et al., “Quantitative pneumatic otoscopy using a light-based ranging technique,” J. Assoc. Res. Otolaryngol. 18(4), 555–568 (2017). http://dx.doi.org/10.1007/s10162-017-0629-5 Google Scholar

87. P. Pande et al., “A mosaicking approach for in vivo thickness mapping of the human tympanic membrane using low coherence interferometry,” J. Assoc. Res. Otolaryngol. 17(5), 403–416 (2016). http://dx.doi.org/10.1007/s10162-016-0576-6 Google Scholar

88. P. Pande et al., “Sensor-based technique for manually scanned hand-held optical coherence tomography imaging,” J. Sens. 2016(1), 1–7 (2016). http://dx.doi.org/10.1155/2016/8154809 Google Scholar

89. L. Hall-Stoodley et al., “Direct detection of bacterial biofilms on the middle-ear mucosa of children with chronic otitis media,” J. Am. Med. Assoc. 296(2), 202–211 (2006).JAMAAP0098-7484 http://dx.doi.org/10.1001/jama.296.2.202 Google Scholar

90. A. M. Zysk et al., “Clinical feasibility of microscopically-guided breast needle biopsy using a fiber-optic probe with computer-aided detection,” Technol. Cancer Res. Treat. 8(5), 315–321 (2009). http://dx.doi.org/10.1177/153303460900800501 Google Scholar

91. W. Luo et al., “Optical biopsy of lymph node morphology using optical coherence tomography,” Technol. Cancer Res. Treat. 4(5), 539–547 (2005). http://dx.doi.org/10.1177/153303460500400507 Google Scholar

92. W. C. Kuo et al., “Real-time three-dimensional optical coherence tomography image-guided core-needle biopsy system,” Biomed. Opt. Express 3(1), 1149–1161 (2012). http://dx.doi.org/10.1364/BOE.3.001149 Google Scholar

93. G. J. McLellan and C. A. Rasmussen, “Optical coherence tomography for the evaluation of retinal and optic nerve morphology in animal subjects: practical considerations,” Vet. Ophthalmol. 15(Suppl. 2), 13–28 (2012). http://dx.doi.org/10.1111/vop.2012.15.issue-s2 Google Scholar

94. R. Powell et al., “Improving magnetic resonance imaging (MRI) examinations: development and evaluation of an intervention to reduce movement in scanners and facilitate scan completion,” Br. J. Health Psychol. 20(3), 449–465 (2015). http://dx.doi.org/10.1111/bjhp.2015.20.issue-3 Google Scholar

95. J. F. Barrett and N. Keat, “Artifacts in CT: recognition and avoidance,” RadioGraphics 24(6), 1679–1691 (2004). http://dx.doi.org/10.1148/rg.246045065 Google Scholar

96. H. Kandpal et al., “Respiratory-triggered versus breath-hold diffusion-weighted MRI of liver lesions: comparison of image quality and apparent diffusion coefficient values,” Am. J. Roentgenol. 192(4), 915–922 (2009). http://dx.doi.org/10.2214/AJR.08.1260 Google Scholar

97. C. J. Kellenberger, S.-J. Yoo and E. R. V. Büchel, “Cardiovascular MR imaging in neonates and infants with congenital heart disease,” RadioGraphics 27(1), 5–18 (2007). http://dx.doi.org/10.1148/rg.271065027 Google Scholar

98. I. Grulkowski et al., “High-precision, high-accuracy ultralong-range swept-source optical coherence tomography using vertical cavity surface emitting laser light source,” Opt. Lett. 38(5), 673–675 (2013).OPLEDP0146-9592 http://dx.doi.org/10.1364/OL.38.000673 Google Scholar

99. T. Klein and R. Huber, “High-speed OCT light sources and systems,” Biomed. Opt. Express 8(2), 828–859 (2017).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.8.000828 Google Scholar

100. N. D. Shemonski et al., “Stability in computed optical interferometric tomography (Part I): stability requirements,” Opt. Express 22(16), 19183–19197 (2014).OPEXFF1094-4087 http://dx.doi.org/10.1364/OE.22.019183 Google Scholar

101. S. I. Balendra et al., “Advances in retinal ganglion cell imaging,” Eye 29(10), 1260–1269 (2015).12ZYAS0950-222X http://dx.doi.org/10.1038/eye.2015.154 Google Scholar

102. J. Polans et al., “Wide-field retinal optical coherence tomography with wavefront sensorless adaptive optics for enhanced imaging of targeted regions,” Biomed. Opt. Express 8(1), 16–37 (2017).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.8.000016 Google Scholar

103. J. P. Kolb et al., “Ultra-widefield retinal MHz-OCT imaging with up to 100 degrees viewing angle,” Biomed. Opt. Express 6(5), 1534–1552 (2015).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.6.001534 Google Scholar

104. A. Roorda et al., “Adaptive optics scanning laser ophthalmoscopy,” Opt. Express 10(9), 405–412 (2002).OPEXFF1094-4087 http://dx.doi.org/10.1364/OE.10.000405 Google Scholar

105. Y. K. Tao and J. A. Izatt, “Spectrally encoded confocal scanning laser ophthalmoscopy,” Opt. Lett. 35(4), 574–576 (2010).OPLEDP0146-9592 http://dx.doi.org/10.1364/OL.35.000574 Google Scholar

106. F. Felberer et al., “Imaging of retinal vasculature using adaptive optics SLO/OCT,” Biomed. Opt. Express 6(4), 1407–1418 (2015).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.6.001407 Google Scholar

107. F. Felberer et al., “Adaptive optics SLO/OCT for 3D imaging of human photoreceptors in vivo,” Biomed. Opt. Express 5(2), 439–456 (2014).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.5.000439 Google Scholar

108. F. LaRocca et al., “Handheld simultaneous scanning laser ophthalmoscopy and optical coherence tomography system,” Biomed. Opt. Express 4(11), 2307–2321 (2013).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.4.002307 Google Scholar

109. D. Nankivil et al., “Handheld, rapidly switchable, anterior/posterior segment swept source optical coherence tomography probe,” Biomed. Opt. Express 6(11), 4516–4528 (2015).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.6.004516 Google Scholar

110. F. LaRocca et al., “In vivo cellular-resolution retinal imaging in infants and children using an ultracompact handheld probe,” Nat. Photonics 10(9), 580–584 (2016).NPAHBY1749-4885 http://dx.doi.org/10.1038/nphoton.2016.141 Google Scholar

111. C. D. Lu et al., “Handheld ultrahigh speed swept source optical coherence tomography instrument using a MEMS scanning mirror,” Biomed. Opt. Express 5(1), 293–311 (2014).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.5.000293 Google Scholar

112. Y. Jia et al., “Quantitative optical coherence tomography angiography of vascular abnormalities in the living human eye,” Proc. Natl. Acad. Sci. U. S. A. 112(18), E2395–E2402 (2015). http://dx.doi.org/10.1073/pnas.1500185112 Google Scholar

113. K. V. Chalam and K. Sambhav, “Optical coherence tomography angiography in retinal diseases,” J. Ophthalmic Vision Res. 11(1), 84–92 (2016). http://dx.doi.org/10.4103/2008-322X.180709 Google Scholar

114. J. L. Yang et al., “Handheld optical coherence tomography angiography,” Biomed. Opt. Express 8(4), 2287–2300 (2017).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.8.002287 Google Scholar

115. “Bioptigen Envisu SDOCT used in rare elephant cataract surgery,” 2012,  http://www.octnews.org/articles/3417664/bioptigen-envisu-sdoct-used-in-rare-elephant-catar/ (June 2017). Google Scholar

116. T. S. Kirtane and M. S. Wagh, “Endoscopic optical coherence tomography (OCT): advances in gastrointestinal imaging,” Gastroenterol. Res. Practice 2014(1), 1–7 (2014). http://dx.doi.org/10.1155/2014/376367 Google Scholar

117. C. Duan et al., “Optical coherence tomography endoscopic probe based on a tilted MEMS mirror,” Biomed. Opt. Express 7(9), 3345–3354 (2016).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.7.003345 Google Scholar

118. M. J. Gora et al., “Endoscopic optical coherence tomography: technologies and clinical applications,” Biomed. Opt. Express 8(5), 2405–2444 (2017).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.8.002405 Google Scholar

119. R. A. McLaughlin, D. Lorenser, D. D. Sampson, “Needle probes in optical coherence tomography,” in Handbook of Coherent-Domain Optical Methods: Biomedical Diagnostics, Environmental Monitoring, and Materials Science, and V. V. Tuchin, Ed., pp. 1065–1102, Springer, New York (2013). Google Scholar

120. T.-H. Tsai, J. G. Fujimoto and H. Mashimo, “Endoscopic optical coherence tomography for clinical gastroenterology,” Diagnostics 4(2), 57–93 (2014). http://dx.doi.org/10.3390/diagnostics4020057 Google Scholar

121. E. B. a la Guillaume et al., “High-resolution handheld rigid endomicroscope based on full-field optical coherence tomography,” J. Biomed. Opt. 21(2), 026005 (2016).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.JBO.21.2.026005 Google Scholar

122. C. A. Coughlan et al., “In vivo cross-sectional imaging of the phonating larynx using long-range Doppler optical coherence tomography,” Sci. Rep. 6(1), 22792 (2016). http://dx.doi.org/10.1038/srep22792 Google Scholar

123. M. J. Gora et al., “Tethered capsule endomicroscopy enables less invasive imaging of gastrointestinal tract microstructure,” Nat. Med. 19(2), 238–240 (2013).1078-8956 http://dx.doi.org/10.1038/nm.3052 Google Scholar

124. M. J. Gora et al., “Tethered capsule endomicroscopy: from bench to bedside at a primary care practice,” J. Biomed. Opt. 21(10), 104001 (2016).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.JBO.21.10.104001 Google Scholar

125. A. Latrive and A. C. Boccara, “In vivo and in situ cellular imaging full-field optical coherence tomography with a rigid endoscopic probe,” Biomed. Opt. Express 2(10), 2897–2904 (2011).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.2.002897 Google Scholar

126. S. Donner et al., “Automated working distance adjustment enables optical coherence tomography of the human larynx in awake patients,” J. Med. Imaging 2(2), 026003 (2015).JMEIET0920-5497 http://dx.doi.org/10.1117/1.JMI.2.2.026003 Google Scholar

127. B. G. Muller et al., “Prostate cancer diagnosis: the feasibility of needle-based optical coherence tomography,” J. Med. Imaging 2(3), 037501 (2015).JMEIET0920-5497 http://dx.doi.org/10.1117/1.JMI.2.3.037501 Google Scholar

128. P. G. K. Wagstaff et al., “Percutaneous needle based optical coherence tomography for the differentiation of renal masses: a pilot cohort,” J. Urol. 195(5), 1578–1585 (2016). http://dx.doi.org/10.1016/j.juro.2015.12.072 Google Scholar

129. C.-P. Liang et al., “A forward-imaging needle-type OCT probe for image guided stereotactic procedures,” Opt. Express 19(27), 26283–26294 (2011).OPEXFF1094-4087 http://dx.doi.org/10.1364/OE.19.026283 Google Scholar

130. Q. Tang et al., “Real-time epidural anesthesia guidance using optical coherence tomography needle probe,” Quant. Imaging Med. Surg. 5(1), 118–124 (2015). http://dx.doi.org/10.3978/j.issn.2223-4292.2014.11.28 Google Scholar

131. M. Villiger et al., “Deep tissue volume imaging of birefringence through fibre-optic needle probes for the delineation of breast tumour,” Sci. Rep. 6(1), 28771 (2016). http://dx.doi.org/10.1038/srep28771 Google Scholar

132. R. A. McLaughlin et al., “Static and dynamic imaging of alveoli using optical coherence tomography needle probes,” J. Appl. Physiol. 113(6), 967–974 (2012). http://dx.doi.org/10.1152/japplphysiol.00051.2012 Google Scholar

133. X. Liang, V. Crecea and S. A. Boppart, “Dynamic optical coherence elastography: a review,” J. Innovative Opt. Health Sci. 3(4), 221–233 (2010). http://dx.doi.org/10.1142/S1793545810001180 Google Scholar

134. X. Liang et al., “Dynamic spectral-domain optical coherence elastography for tissue characterization,” Opt. Express 18(13), 14183–14190 (2010).OPEXFF1094-4087 http://dx.doi.org/10.1364/OE.18.014183 Google Scholar

135. K. M. Kennedy et al., “Quantitative micro-elastography: imaging of tissue elasticity using compression optical coherence elastography,” Sci. Rep. 5(1), 15538 (2015). http://dx.doi.org/10.1038/srep15538 Google Scholar

136. B. F. Kennedy, P. Wijesinghe and D. D. Sampson, “The emergence of optical elastography in biomedicine,” Nat. Photonics 11(4), 215–221 (2017).NPAHBY1749-4885 http://dx.doi.org/10.1038/nphoton.2017.6 Google Scholar

137. P.-C. Huang et al., “Quantitative characterization of mechanically indented in vivo human skin in adults and infants using optical coherence tomography,” J. Biomed. Opt. 22(3), 034001 (2017).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.JBO.22.3.034001 Google Scholar

138. K. M. Kennedy et al., “Needle optical coherence elastography for tissue boundary detection,” Opt. Lett. 37(12), 2310–2312 (2012).OPLEDP0146-9592 http://dx.doi.org/10.1364/OL.37.002310 Google Scholar

139. G. J. Tearney et al., “Catheter-based optical imaging of a human coronary artery,” Circulation 94(11), 3013–3013 (1996).CIRCAZ0009-7322 http://dx.doi.org/10.1161/01.CIR.94.11.3013 Google Scholar

140. J. G. Fujimoto et al., “High resolution in vivo intra-arterial imaging with optical coherence tomography,” Heart 82(2), 128–133 (1999). http://dx.doi.org/10.1136/hrt.82.2.128 Google Scholar

141. M. Atif et al., “Catheters for optical coherence tomography,” Laser Phys. Lett. 8(9), 629–646 (2011).1612-2011 http://dx.doi.org/10.1002/lapl.201110035 Google Scholar

142. A. Maehara et al., “Comparison of stent expansion guided by optical coherence tomography versus intravascular ultrasound,” Cardiovasc. Interventions 8(13), 1704–1714 (2015). http://dx.doi.org/10.1016/j.jcin.2015.07.024 Google Scholar

143. K. Rathod et al., “Intravascular ultrasound versus optical coherence tomography for coronary artery imaging–apples to oranges?” Interventional Cardiol. Rev. 10(1), 8–15 (2015). http://dx.doi.org/10.15420/icr.2015.10.1.8 Google Scholar

144. M. Terashima, H. Kaneda and T. Suzuki, “The role of optical coherence tomography in coronary intervention,” Korean J. Intern. Med. 27(1), 1–12 (2012).KJIMEH http://dx.doi.org/10.3904/kjim.2012.27.1.1 Google Scholar

145. Z. A. Ali et al., “Optical coherence tomography compared with intravascular ultrasound and with angiography to guide coronary stent implantation (ILUMIEN III: OPTIMIZE PCI): a randomised controlled trial,” Lancet 388(10060), 2618–2628 (2016).LANCAO0140-6736 http://dx.doi.org/10.1016/S0140-6736(16)31922-5 Google Scholar

146. L. Vignali, E. Solinas and E. Emanuele, “Research and clinical applications of optical coherence tomography in invasive cardiology: a review,” Curr. Cardiol. Rev. 10(4), 369–376 (2014). http://dx.doi.org/10.2174/1573403X10666140604120753 Google Scholar

147. T. Roleder et al., “The basics of intravascular optical coherence tomography,” Adv. Interventional Cardiol. 11(2), 74–83 (2015). http://dx.doi.org/10.5114/pwki.2015.52278 Google Scholar

148. M. A. ul Haq et al., “The invasive assessment of coronary atherosclerosis and stents using optical coherence tomography: a clinical update,” Heart Asia 5(1), 154–161 (2013). http://dx.doi.org/10.1136/heartasia-2013-010328 Google Scholar

149. M. Machoy et al., “The use of optical coherence tomography in dental diagnostics: a state-of-the-art review,” J. Healthcare Eng. 2017(1), 1–31 (2017). http://dx.doi.org/10.1155/2017/7560645 Google Scholar

150. C.-K. Lee et al., “Diagnosis of oral precancer with optical coherence tomography,” Biomed. Opt. Express 3(7), 1632–1646 (2012).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.3.001632 Google Scholar

151. P. Pande et al., “Automated classification of optical coherence tomography images for the diagnosis of oral malignancy in the hamster cheek pouch,” J. Biomed. Opt. 19(8), 086022 (2014).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.JBO.19.8.086022 Google Scholar

152. H. Schneider et al., “Dental applications of optical coherence tomography (OCT) in cariology,” Appl. Sci. 7(472), 1–21 (2017). http://dx.doi.org/10.3390/app7050472 Google Scholar

153. M. S. Segarra et al., “Three-dimensional analysis of enamel crack behavior using optical coherence tomography,” J. Dent. Res. 96(3), 308–314 (2017).JDREAF0022-0345 http://dx.doi.org/10.1177/0022034516680156 Google Scholar

154. D. Demian et al., “Design and testing of prototype handheld scanning probes for optical coherence tomography,” Proc. Inst. Mech. Eng.: Part H. 228(8), 743–753 (2014). http://dx.doi.org/10.1177/0954411914543963 Google Scholar

155. V. F. Duma et al., “Handheld scanning probes for optical coherence tomography: developments, applications, and perspectives,” Proc. SPIE 9670, 96700V (2016).PSISDG0277-786X http://dx.doi.org/10.1117/12.2178590 Google Scholar

156. P. Lenton et al., “Clinical cross-polarization optical coherence tomography assessment of subsurface enamel below dental resin composite restorations,” J. Med. Imaging 1(1), 016001 (2014).JMEIET0920-5497 http://dx.doi.org/10.1117/1.JMI.1.1.016001 Google Scholar

157. A. J. Coleman et al., “Histological correlates of optical coherence tomography in non-melanoma skin cancer,” Skin Res. Technol. 19(1), e10–e19 (2013). http://dx.doi.org/10.1111/j.1600-0846.2012.00626.x Google Scholar

158. M. Ulrich et al., “Dynamic optical coherence tomography in dermatology,” Dermatology 232(3), 298–311 (2016).DERMEI0742-3217 http://dx.doi.org/10.1159/000444706 Google Scholar

159. E. Sattler, R. Kästle and J. Welzel, “Optical coherence tomography in dermatology,” J. Biomed. Opt. 18(6), 061224 (2013).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.JBO.18.6.061224 Google Scholar

160. P. Su et al., “In vivo high-definition optical coherence tomography: a bedside diagnostic aid for morphea,” JAMA Dermatol. 151(2), 234–235 (2015). http://dx.doi.org/10.1001/jamadermatol.2014.2668 Google Scholar

161. U. Baran et al., “High resolution imaging of acne lesion development and scarring in human facial skin using OCT-based microangiography,” Lasers Surg. Med. 47(3), 231–238 (2015).LSMEDI0196-8092 http://dx.doi.org/10.1002/lsm.v47.3 Google Scholar

162. N. De Carvalho et al., “In vivo micro-angiography by means of speckle-variance optical coherence tomography (SV-OCT) is able to detect microscopic vascular changes in naevus to melanoma transition,” J. Eur. Acad. Dermatol. Venereol. 30(10), e67–e68 (2016).JEAVEQ0926-9959 http://dx.doi.org/10.1111/jdv.2016.30.issue-10 Google Scholar

163. A. Cogliati et al., “MEMS-based handheld scanning probe with pre-shaped input signals for distortion-free images in Gabor-domain optical coherence microscopy,” Opt. Express 24(12), 13365–13374 (2016).OPEXFF1094-4087 http://dx.doi.org/10.1364/OE.24.013365 Google Scholar

164. L. Themstrup et al., “In vivo microvascular imaging of cutaneous actinic keratosis, Bowen’s disease and squamous cell carcinoma using dynamic optical coherence tomography,” J. Eur. Acad. Dermatol. Venereol. 31(10), 1655–1662 (2017).JEAVEQ0926-9959 http://dx.doi.org/10.1111/jdv.2017.31.issue-10 Google Scholar

165. O. M. Carrasco-Zevallos et al., “Review of intraoperative optical coherence tomography: technology and applications,” Biomed. Opt. Express 8(3), 1607–1637 (2017).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.8.001607 Google Scholar

166. H. Yu et al., “Evaluation of microsurgical tasks with OCT-guided and/or robot-assisted ophthalmic forceps,” Biomed. Opt. Express 6(2), 457–472 (2015).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.6.000457 Google Scholar

167. C. Song, P. L. Gehlbach and J. U. Kang, “Active tremor cancellation by a ‘SMART’ handheld vitreoretinal microsurgical tool using swept source optical coherence tomography,” Opt. Express 20(21), 23414–23421 (2012).OPEXFF1094-4087 http://dx.doi.org/10.1364/OE.20.023414 Google Scholar

168. Y. Huang et al., “MEMS-based handheld Fourier domain doppler optical coherence tomography for intraoperative microvascular anastomosis imaging,” PLoS One 9(12), e114215 (2014).POLNCL1932-6203 http://dx.doi.org/10.1371/journal.pone.0114215 Google Scholar

169. K. M. Joos and J.-H. Shen, “Miniature real-time intraoperative forward-imaging optical coherence tomography probe,” Biomed. Opt. Express 4(8), 1342–1350 (2013).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.4.001342 Google Scholar

170. G. J. Tearney et al., “Determination of the refractive index of highly scattering human tissue by optical coherence tomography,” Opt. Lett. 20(21), 2258–2260 (1995).OPLEDP0146-9592 http://dx.doi.org/10.1364/OL.20.002258 Google Scholar

171. T. M. Lee et al., “Engineered microsphere contrast agents for optical coherence tomography,” Opt. Lett. 28(17), 1546–1548 (2003).OPLEDP0146-9592 http://dx.doi.org/10.1364/OL.28.001546 Google Scholar

172. B. W. Graf et al., “In vivo multimodal microscopy for detecting bone-marrow-derived cell contribution to skin regeneration,” J. Biophotonics 7(1–2), 96–102 (2014). http://dx.doi.org/10.1002/jbio.v7.1/2 Google Scholar

173. C. V. Raman and K. S. Krishnan, “A new type of secondary radiation,” Nature 121(3048), 501–502 (1928). http://dx.doi.org/10.1038/121501c0 Google Scholar

174. K. Kong et al., “Raman spectroscopy for medical diagnostics–from in vitro biofluid assays to in vivo cancer detection,” Adv. Drug Delivery Rev. 89(1), 121–134 (2015).ADDREP0169-409X http://dx.doi.org/10.1016/j.addr.2015.03.009 Google Scholar

175. C. A. Patil et al., “A clinical instrument for combined raman spectroscopy-optical coherence tomography of skin cancers,” Lasers Surg. Med. 43(2), 143–151 (2011).LSMEDI0196-8092 http://dx.doi.org/10.1002/lsm.v43.2 Google Scholar

176. J. Wang et al., “Development of a hybrid Raman spectroscopy and optical coherence tomography technique for real-time in vivo tissue measurements,” Opt. Lett. 41(13), 3045–3048 (2016).OPLEDP0146-9592 http://dx.doi.org/10.1364/OL.41.003045 Google Scholar

177. C. A. Patil et al., “Integrated system for combined Raman spectroscopy-spectral domain optical coherence tomography,” J. Biomed. Opt. 16(1), 011007 (2011).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.3520132 Google Scholar

178. Y. Zhao et al., “Rapid diagnosis and differentiation of microbial pathogens in otitis media with a combined Raman spectroscopy and low-coherence interferometry probe: toward in vivo implementation,” J. Biomed. Opt. 21(10), 107005 (2016).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.JBO.21.10.107005 Google Scholar

179. H. Yoo et al., “Intra-arterial catheter for simultaneous microstructural and molecular imaging in vivo,” Nat. Med. 17(12), 1680–1684 (2011).1078-8956 http://dx.doi.org/10.1038/nm.2555 Google Scholar

180. S. Liang et al., “Intravascular atherosclerotic imaging with combined fluorescence and optical coherence tomography probe based on a double-clad fiber combiner,” J. Biomed. Opt. 17(7), 070501 (2012).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.JBO.17.7.070501 Google Scholar

181. A. R. Tumlinson et al., “Miniature endoscope for simultaneous optical coherence tomography and laser-induced fluorescence measurement,” Appl. Opt. 43(1), 113–121 (2004).APOPAI0003-6935 http://dx.doi.org/10.1364/AO.43.000113 Google Scholar

182. J. Mavadia et al., “An all-fiber-optic endoscopy platform for simultaneous OCT and fluorescence imaging,” Biomed. Opt. Express 3(11), 2851–2859 (2012).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.3.002851 Google Scholar

183. N. Iftimia et al., “Handheld optical coherence tomography-reflectance confocal microscopy probe for detection of basal cell carcinoma and delineation of margins,” J. Biomed. Opt. 22(7), 076006 (2017).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.JBO.22.7.076006 Google Scholar

184. J. Yin et al., “Integrated intravascular optical coherence tomography ultrasound imaging system,” J. Biomed. Opt. 15(1), 010512 (2010).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.3308642 Google Scholar

185. H. C. Yang et al., “A dual-modality probe utilizing intravascular ultrasound and optical coherence tomography for intravascular imaging applications,” IEEE Trans. Ultrason. Ferroelectr. Freq. Control 57(12), 2839–2843 (2010). http://dx.doi.org/10.1109/TUFFC.2010.1758 Google Scholar

186. X. Dai et al., “Miniature endoscope for multimodal imaging,” ACS Photonics 4(1), 174–180 (2017). http://dx.doi.org/10.1021/acsphotonics.6b00852 Google Scholar

187. R. E. Wijesinghe et al., “Optical coherence tomography-integrated, wearable (backpack-type), compact diagnostic imaging modality for in situ leaf quality assessment,” Appl. Opt. 56(9), D108–D114 (2017).APOPAI0003-6935 http://dx.doi.org/10.1364/AO.56.00D108 Google Scholar

188. R. Su et al., “Perspectives of mid-infrared optical coherence tomography for inspection and micrometrology of industrial ceramics,” Opt. Express 22(13), 15804–15819 (2014).OPEXFF1094-4087 http://dx.doi.org/10.1364/OE.22.015804 Google Scholar

189. M. Shirazi et al., “Fast industrial inspection of optical thin film using optical coherence tomography,” Sensors 16(1598), 1–13 (2016).SNSRES0746-9462 http://dx.doi.org/10.3390/s16101598 Google Scholar

190. R. D. Harris and W. M. Marks, “Compact ultrasound for improving maternal and perinatal care in low-resource settings,” J. Ultrasound Med. 28(8), 1067–1076 (2009).JUMEDA0278-4297 http://dx.doi.org/10.7863/jum.2009.28.8.1067 Google Scholar

191. D. S.-R. Maru et al., “Turning a blind eye: the mobilization of radiology services in resource-poor regions,” Globalization Health 6(18), 1–8 (2010). http://dx.doi.org/10.1186/1744-8603-6-18 Google Scholar

192. S. Sharma et al., “Point-of-care diagnostics in low resource settings: present status and future role of microfluidics,” Biosensors 5(1), 577–601 (2015).BISSED0265-928X http://dx.doi.org/10.3390/bios5030577 Google Scholar

193. A. Yurt et al., “Towards practical cost-effective lens-free imaging,” Proc. SPIE 10055, 100550J (2017). http://dx.doi.org/10.1117/12.2253237 Google Scholar

194. R. Richards-Kortum and M. Oden, “Devices for low-resource health care,” Science 342(6162), 1055–1057 (2013).SCIEAS0036-8075 http://dx.doi.org/10.1126/science.1243473 Google Scholar

195. S. A. Boppart and R. Richards-Kortum, “Point-of-care and point-of-procedure optical imaging technologies for primary care and global health,” Sci. Transl. Med. 6(253), 253rv2 (2014). http://dx.doi.org/10.1126/scitranslmed.3009725 Google Scholar

196. V. T. Tran and P. Ravaud, “Frugal innovation in medicine for low resource settings,” BMC Med. 14(102), 1–3 (2016). http://dx.doi.org/10.1186/s12916-016-0651-1 Google Scholar

197. A. Wong et al., “The role of optical coherence tomography raster imaging as a valuable diagnostic tool in the differential between optic disc hemorrhage and vitreopapillary traction,” Mil. Med. 177(11), 1374–1381 (2012).MMEDA90026-4075 http://dx.doi.org/10.7205/MILMED-D-12-00148 Google Scholar

198. V. Fathipour et al., “Demonstration of shot-noise-limited swept source OCT without balanced detection,” Sci. Rep. 7(1), 1183 (2017). http://dx.doi.org/10.1038/s41598-017-01339-6 Google Scholar

199. K. Neuhaus et al., “Comparing an FFT filter for multiple reference optical coherence tomography (MR-OCT) with an Chebychev and an elliptic filter,” Proc. SPIE 10055, 100550X (2017). http://dx.doi.org/10.1117/12.2253265 Google Scholar

200. K. Osawa et al., “Low cost, high resolution optical coherence tomography utilizing a narrowband laser diode,” Proc. SPIE 9312, 931237 (2015).PSISDG0277-786X http://dx.doi.org/10.1117/12.2074244 Google Scholar

201. S. Moon and E. S. Choi, “VCSEL-based swept source for low-cost optical coherence tomography,” Biomed. Opt. Express 8(2), 1110–1121 (2017).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.8.001110 Google Scholar

202. C. C. Rosa et al., “Multiscan time-domain optical coherence tomography for retina imaging,” Appl. Opt. 46(10), 1795–1808 (2007).APOPAI0003-6935 http://dx.doi.org/10.1364/AO.46.001795 Google Scholar

203. M. R. N. Avanaki and A. Podoleanu, “En-face time-domain optical coherence tomography with dynamic focus for high-resolution imaging,” J. Biomed. Opt. 22(5), 056009 (2017).JBOPFO1083-3668 http://dx.doi.org/10.1117/1.JBO.22.5.056009 Google Scholar

204. R. Leitgeb, C. Hitzenberger and A. Fercher, “Performance of Fourier domain vs. time domain optical coherence tomography,” Opt. Express 11(8), 889–894 (2003).OPEXFF1094-4087 http://dx.doi.org/10.1364/OE.11.000889 Google Scholar

205. P. Pande et al., “Low-cost hand-held probe for depth-resolved low-coherence interferometry,” Biomed. Opt. Express 8(1), 338–348 (2017).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.8.000338 Google Scholar

206. P. Koch, V. Hellemanns and G. Hüttmann, “Linear optical coherence tomography system with extended measurement range,” Opt. Lett. 31(19), 2882–2884 (2006).OPLEDP0146-9592 http://dx.doi.org/10.1364/OL.31.002882 Google Scholar

207. R. Dsouza et al., “Dermascope guided multiple reference optical coherence tomography,” Biomed. Opt. Express 5(9), 2870–2882 (2014).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.5.002870 Google Scholar

208. M. J. Leahy et al., “The how and why of a $10 optical coherence tomography system,” Proc. SPIE 9697, 96970T (2016).PSISDG0277-786X http://dx.doi.org/10.1117/12.2213465 Google Scholar

209. B. Gefvert, “Optical coherence tomography: novel design makes OCT more accessible,” in BioOptics World,  http://www.bioopticsworld.com/articles/print/volume-10/issue-5/optical-coherence-tomography-novel-design-makes-oct-more-accessible.html (June 2017). Google Scholar

210. V. D. Nguyen et al., “Spectral domain optical coherence tomography imaging with an integrated optics spectrometer,” Opt. Lett. 36(7), 1293–1295 (2011).OPLEDP0146-9592 http://dx.doi.org/10.1364/OL.36.001293 Google Scholar

211. V. D. Nguyen et al., “Integrated-optics-based swept-source optical coherence tomography,” Opt. Lett. 37(23), 4820–4822 (2012).OPLEDP0146-9592 http://dx.doi.org/10.1364/OL.37.004820 Google Scholar

212. B. I. Akca et al., “Miniature spectrometer and beam splitter for an optical coherence tomography on a silicon chip,” Opt. Express 21(14), 16648–16656 (2013).OPEXFF1094-4087 http://dx.doi.org/10.1364/OE.21.016648 Google Scholar

213. Z. Wang et al., “Silicon photonic integrated circuit swept-source optical coherence tomography receiver with dual polarization, dual balanced, in-phase and quadrature detection,” Biomed. Opt. Express 6(7), 2562–2574 (2015).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.6.002562 Google Scholar

214. G. Yurtsever et al., “Photonic integrated Mach-Zehnder interferometer with an on-chip reference arm for optical coherence tomography,” Biomed. Opt. Express 5(4), 1050–1061 (2014).BOEICL2156-7085 http://dx.doi.org/10.1364/BOE.5.001050 Google Scholar

215. G. Yurtsever et al., “Ultra-compact silicon photonic integrated interferometer for swept-source optical coherence tomography,” Opt. Lett. 39(17), 5228–5231 (2014).OPLEDP0146-9592 http://dx.doi.org/10.1364/OL.39.005228 Google Scholar

216. S. Schneider et al., “Optical coherence tomography system mass-producible on a silicon photonic chip,” Opt. Express 24(2), 1573–1586 (2016).OPEXFF1094-4087 http://dx.doi.org/10.1364/OE.24.001573 Google Scholar


Guillermo L. Monroy is currently a graduate research fellow (PhD candidate) at the Biophotonics Imaging Laboratory, working under the guidance of Professor Stephen Boppart. He received his BS degree in computer engineering in 2011, and continued for his MS degree in bioengineering in 2013 from the University of Illinois at Urbana–Champaign. His current academic interests include the integration of advanced biomedical instrumentation and imaging techniques to improve diagnosis and treatment in healthcare.

Jungeun Won is a graduate student working toward her PhD in bioengineering at the Biophotonics Imaging Laboratory, working under the guidance of Professor Stephen Boppart. She received her BS degree in biomedical engineering in 2015 from the University of Rochester, and received her MS degree in bioengineering in 2017 from the University of Illinois at Urbana–Champaign. Her research interests include developing optical imaging systems and analytic methods to improve medical diagnosis.

Darold R. Spillman Jr. received his associate of arts degree in human resources from the Community College of the Air Force, Maxwell AFB, Georgia in 2005 and his BA degree in general studies from Eastern Illinois University, Charleston, Illinois in 2015. He served in the United State Air Force from 1984 to 2007. He was a 1993 Presidential Point of Light Award nominee and was spotlighted in an inside Illinois publication in 2011.

Roshan Dsouza is currently a postdoctoral researcher at the Beckman Institute for Advance Science and Technology, University of Illinois at Urbana–Champaign. He received his master’s degree in photonics from Manipal University, India, in 2011 and his PhD in biomedical optics from the National University of Ireland, Galway, in 2016. His research interests include the development of low-cost imaging devices and biophotonics applications in low-resource settings.

Stephen A. Boppart received his BS degree in electrical engineering with an option in bioengineering and his MS degree in electrical engineering from the University of Illinois at Urbana–Champaign, Urbana, Illinois, in 1990 and 1991, respectively, his PhD in electrical and medical engineering from Massachusetts Institute of Technology, Cambridge, in 1998, and his MD degree from Harvard Medical School, Boston, Massachusetts, in 2000. Currently, he is an Abel Bliss professor of engineering at the Departments of Electrical and Computer Engineering, Bioengineering, and Medicine, the head of the Biophotonics Imaging Laboratory at the Beckman Institute for Advanced Science and Technology, University of Illinois at Urbana–Champaign, and the director of the Center for Optical Molecular Imaging. His research interests include the development of novel optical imaging technologies for biological and medical applications, with particular emphasis on translating these to clinical applications. He is a fellow of SPIE, AAAS, IEEE, OSA, BMES, and AIMBE.

© The Authors. Published by SPIE under a Creative Commons Attribution 3.0 Unported License. Distribution or reproduction of this work in whole or in part requires full attribution of the original publication, including its DOI.
Guillermo L. Monroy, Jungeun Won, Darold R. Spillman, Roshan Dsouza, Stephen A. Boppart, "Clinical translation of handheld optical coherence tomography: practical considerations and recent advancements," Journal of Biomedical Optics 22(12), 121715 (19 December 2017). https://doi.org/10.1117/1.JBO.22.12.121715 Submission: Received 6 October 2017; Accepted 4 December 2017
Submission: Received 6 October 2017; Accepted 4 December 2017

Optical coherence tomography

Imaging systems


Computer aided design


In vivo imaging


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