Abstract: Techniques for collecting and processing complex OCT data to detect localized motion contrast information with enhanced accuracy and sensitivity are presented. In a preferred embodiment, vector differences between complex OCT signals taken at the same location on the sample are used to detect blood flow in the retina. Additional embodiments involving non-linear intensity weighting of the motion contrast information, normalization of the vector difference amplitudes, and calculating the absolute value of the standard deviation of Doppler signal are described. Image processing techniques to enhance the images resulting from these motion contrast techniques are also presented.

Abstract: A surgical imaging system can comprise a light source, configured to generate an imaging light beam; a beam guidance system, configured to guide the imaging light beam from the light source; a beam scanner, configured to receive the imaging light from the beam guidance system, and to generate a scanned imaging light beam; a beam coupler, configured to redirect the scanned imaging light beam; and a wide field of view (WFOV) lens, configured to guide the redirected scanned imaging light beam into a target region of a procedure eye.

Abstract: Devices, systems, and methods that utilize a technique of changing a position of the set of optical fibers of the fiber bundle in cooperation with the scanning of the imaging light across a proximal surface of the fiber bundle to improve the resolution of the scanned image. In particular, a bundle actuator can be provided to change a position of the set of optical fibers of the fiber bundle in cooperation with a scanning of the imaging light across the proximal surface of the fiber bundle to cover the areas of the gaps between the optical fibers and to increase a resolution of the scanned image.

Abstract: An optical light scanning probe is presented, the probe comprising a handle, shaped for grasping by a user; a cannula, protruding from a distal portion of the handle with an outer diameter smaller than 20 gauge; an optical fiber with a distal fiber-portion off a probe-axis, configured to receive a light from a light-source at a proximal fiber-portion, and to emit the received light at the distal fiber-portion; a fixed beam forming unit, disposed at a distal portion of the cannula, configured to receive the light from the distal fiber-portion, and to deflect the received light toward a target region; and a fiber actuator, housed at least partially in the handle, configured to move the distal fiber-portion to scan the deflected light along a scanning curve in the target region.

Abstract: An ophthalmic surgical tool has a marker positioned at a distal portion of the ophthalmic surgical tool. The distal portion of the ophthalmic surgical tool is inserted into an eye along with the marker to perform surgeries in the eye. An imaging device captures images of the fundus of the eye including the distal portion of the ophthalmic surgical tool. An image processor processes the captured images to identify and extract the marker from the captured images. The marker has a high-contrast feature in a visible light or infrared light range or other spectral ranges. Thus, the image processor may identify and extract the marker from the captured images. Indicators may be generated based on the marker and be overlaid with the captured or processed images of the fundus and displayed to a user to indicate surgical information to the user.

Abstract: An optical scanning probe comprises a handle to receive a light beam from a light guide; a cannula, extending from a distal end of the handle; a fiber, positioned partially inside the handle and partially inside the cannula, to guide the received light beam toward a distal end of the cannula; a rotating scanner, rotatably positioned at least partially inside the cannula and configured to house a proximal portion of the fiber; and a deflecting scanner, movably coupled to a distal end of the rotating scanner, configured to deflect a distal portion of the fiber, wherein the distal portion of the fiber is configured to emit and scan the guided light in a target region.

Abstract: A Slit-lamp-or-Microscope-Integrated-OCT-Refractometer system includes an eye-visualization system, configured to provide a visual image of an imaged region in an eye; an Optical Coherence Tomographic (OCT) imaging system, configured to generate an OCT image of the imaged region; a refractometer, configured to generate a refractive mapping of the imaged region; and an analyzer, configured to determine refractive characteristics of the eye based on the OCT image and the refractive mapping, wherein the refractometer and the OCT imaging system are integrated into the eye visualization system.

Abstract: Systems and methods for capturing intraoperative biometry and/or refractive measurements include a sensor or valve associated with the eye and configured to detect a pressure of the eye. The system also includes an intra-op diagnostics device including a control unit arranged to actuate the intra-op diagnostics device to capture the intraoperative biometry and/or refractive measurements when the sensor or valve detects pressure within a predetermined pressure range.

Abstract: Systems and methods for reducing noise in balanced detection based optical coherence tomography (OCT) systems are described. Embodiments including both optical hardware and electronic based solutions to spectrally filter and attenuate the source reference light in optical coherence tomography in an effort to reduce RIN and FPN noise in OCT systems are presented. A novel application to electronic balanced detection schemes in which a single source of reference detection is balanced against the interferometric signals from multiple interferometers is also presented.

Abstract: In certain embodiments, a scanning system comprises optical elements and a movement system. The optical elements comprise an optical fiber and a focusing element. The optical fiber transmits a light ray and has a fiber axis that extends to an imaginary fiber axis. The focusing element refracts the light ray and has a focusing element optical axis that is substantially aligned with the imaginary fiber axis. The movement system rotates the focusing element about the focusing element optical axis to scan the light ray. In other embodiments, a scanning system comprises optical elements and a movement system. The optical elements comprise an optical fiber, a focusing element, and a prism. The prism has a prism optical axis and receives the light ray from the focusing element. The movement system rotates the prism about the prism optical axis to scan the light ray.

Abstract: An adjustment system for an Optical Coherence Tomography (OCT) imaging system includes an OCT light source; a beam splitter, splitting the OCT light beam into an imaging beam to an imaging arm, and a reference beam to a reference arm; a probe, guiding the imaging beam onto a target and receiving a returned imaging beam from the target; the beam splitter generating an interference beam from the returned imaging beam and a returned reference beam from the reference arm; an imaging detector, detecting the interference beam; an imaging processor, generating an OCT image from the detected interference beam; and an adjustment device, removably coupled to the probe, the adjustment device comprising the target attached to a distal region of a target holder at a working distance from a distal end of the imaging probe, wherein an optical length of the reference arm is adjustable to improve a calibration of the OCT image.

Abstract: Systems, methods and applications for adjusting the imaging depth of a Fourier Domain optical coherence tomography system without impacting the axial resolution of the system are presented. One embodiment of the invention involves changing the sweep rate of a swept-source OCT system while maintaining the same data acquisition rate and spectral bandwidth of the source. Another embodiment involves changing the data acquisition rate of a SS-OCT system while maintaining the same sweep rate over the same spectral bandwidth. Several applications of variable imaging depth in the field of ophthalmic imaging are described.

Abstract: Techniques for collecting and processing complex OCT data to detect localized motion contrast information with enhanced accuracy and sensitivity are presented. In a preferred embodiment, vector differences between complex OCT signals taken at the same location on the sample are used to detect blood flow in the retina. Additional embodiments involving non-linear intensity weighting of the motion contrast information, normalization of the vector difference amplitudes, and calculating the absolute value of the standard deviation of Doppler signal are described. Image processing techniques to enhance the images resulting from these motion contrast techniques are also presented.

Abstract: Systems and methods for increasing the duty cycle and/or producing interleaved pulses of alternating polarization states in swept-source optical coherence tomography (OCT) systems are considered. Embodiments including improved buffering, frequency selecting filter sharing among multiple SOAs, intracavity switching, and multiple wavelength bands are described. The unique polarization properties of the source configurations have advantages in speckle reduction, polarization-sensitive measurements, polarization state dependent phase shifts, spatial shifts, and temporal shifts in OCT measurements.

Abstract: Systems and methods for reducing noise in balanced detection based optical coherence tomography (OCT) systems are described. Embodiments including both optical hardware and electronic based solutions to spectrally filter and attenuate the source reference light in optical coherence tomography in an effort to reduce RIN and FPN noise in OCT systems are presented. A novel application to electronic balanced detection schemes in which a single source of reference detection is balanced against the interferometric signals from multiple interferometers is also presented.

Abstract: Techniques for collecting and processing complex OCT data to detect localized motion contrast information with enhanced accuracy and sensitivity are presented. In a preferred embodiment, vector differences between complex OCT signals taken at the same location on the sample are used to detect blood flow in the retina. Additional embodiments involving non-linear intensity weighting of the motion contrast information, normalization of the vector difference amplitudes, and calculating the absolute value of the standard deviation of Doppler signal are described. Image processing techniques to enhance the images resulting from these motion contrast techniques are also presented.

Abstract: Two-dimensional and three-dimensional optical coherence tomography is obtained by differential imaging of full-frame interference images using a white light source. Full-color tomographic imaging is also possible by processing the three-color channels of the interference images. A technique is described to obtain two-dimensional OCT images with full natural color representation. In a particular embodiment, the interference image is acquired using a color camera and the three-color channels are processed separately, recomposing the final image. In an additional embodiment, the interference images are acquired using separate red, blue and green light sources and the three color channels are combined to recompose the final image.

Abstract: Two-dimensional and three-dimensional optical coherence tomography is obtained by differential imaging of full-frame interference images using a white light source. Full-color tomographic imaging is also possible by processing the three-color channels of the interference images. A technique is described to obtain two-dimensional OCT images with full natural color representation. In a particular embodiment, the interference image is acquired using a color camera and the three-color channels are processed separately, recomposing the final image. In an additional embodiment, the interference images are acquired using separate red, blue and green light sources and the three color channels are combined to recompose the final image.

Abstract: Two-dimensional and three-dimensional optical coherence tomography is obtained by differential imaging of full-frame interference images using a white light source. Full-color tomographic imaging is also possible by processing the three-color channels of the interference images. A technique is described to obtain two-dimensional OCT images with full natural color representation. In a particular embodiment, the interference image is acquired using a color camera and the three-color channels are processed separately, recomposing the final image. In an additional embodiment, the interference images are acquired using separate red, blue and green light sources and the three color channels are combined to recompose the final image.