39 results about "Scanning laser ophthalmoscope" patented technology

A combination of a scanning laser ophthalmoscope and external laser sources (52) is used for microphotocoagulation and photodynamic therapy, two examples of selective therapeutic laser. A linkage device incorporating a beamsplitter (56) and collimator-telescope (60) is adjusted to align the pivot point (16) of the scanning lasers (38, 40) and external laser source (52). A similar pivot point minimizes wavefront aberrations, enables precise focusing and registration of the therapeutic laser beam (52) on the retina without the risk of vignetting. One confocal detection pathway of the scanning laser ophthalmoscope images the retina. A second and synchronized detection pathway with a different barrier filter (48) is needed to draw the position and extent of the therapeutic laser spot on the retinal image, as an overlay (64). Advanced spatial modulation increases the selectivity of the therapeutic laser. In microphotocoagulation, an adaptive optics lens (318) is attached to the scanning laser ophthalmoscope, in proximity of the eye. It corrects the higher order optical aberrations of the eye optics, resulting in smaller and better focused applications. In photodynamic therapy, a spatial modulator (420) is placed within the collimator-telescope (60) of the therapeutic laser beam (52), customizing its shape as needed. A similar effect can be obtained by modulating a scanning laser source (38) of appropriate wavelength for photodynamic therapy.

An optical coherence tomography (OCT) system including a polarizing splitter disposed to direct light in an interferometer such that the OCT detector operates in a noise-optimized regime. When scanning an eye, the system detector simultaneously produces a low-frequency component representing a scanning laser ophthalmoscope-like (SLO-like) image pixel and a high frequency component representing a two-dimensional (2D) OCT en face image pixel of each point. The SLO-like image is unchanging with depth, so that the pixels in each SLO-like image may be quickly realigned with the previous SLO-like image by consulting prominent image features (e.g., vessels) should lateral eye motion shift an OCT en face image during recording. Because of the pixel-to-pixel correspondence between the simultaneous OCT and SLO-like images, the OCT image pixels may be remapped on the fly according to the corresponding SLO-like image pixel remapping to create an undistorted 3D image data set for the scanned region.

Real time, high-speed image stabilization with a retinal tracking scanning laser ophthalmoscope (TSLO) enables new approaches to established diagnostics. Large frequency range (DC to 19 kHz), wide-field (40-deg) stabilized Doppler flowmetry imaging is described for human subjects. The fundus imaging method is a quasi-confocal line-scanning laser ophthalmoscope (LSLO). The retinal tracking system uses a confocal reflectometer with a closed loop optical servo system to lock onto features in the ocular fundus and automatically re-lock after blinks. By performing a slow scan with the laser line imager, frequency-resolved retinal perfusion and vascular flow images can be obtained free of eye motion artifacts.

A combination of a confocal scanning laser ophthalmoscope and external laser sources is used for microphotocoagulation purposes. An opto-mechanical linkage device and beamsplitter is used to align the pivot point of the Maxwellian view of the scanning laser ophthalmoscope with the pivot point of non-scanning external laser beams. The same pivot point is necessary to minimize wavefront aberrations and to enable precise focussing of a therapeutic laser beam on the retina. An AOM and / or two-dimensional AOD can be inserted in the pathway of the Gaussian therapeutic beam to control intensity and spatial pattern of small and short-duration pulses. The location of the external laser beam on the retina is determined with the help of two synchronized detectors and image processing. One detector is used to localize moving fiducial landmarks of the retina. A second detector is used to locate on the retina the external laser aiming beam. Two different confocal apertures are used. Polarizing the aiming beam is necessary to further reduce unwanted reflections from the anterior corneal surface.

Methods and devices are disclosed for acquiring depth resolved aberration information using principles of low coherence interferometry and perform coherence gated wavefront sensing (CG-WFS). The wavefront aberrations is collected using spectral domain low coherence interferometry (SD-LCI) or time domain low coherence interferometry (TD-LCI) principles. When using SD-LCI, chromatic aberrations can also be evaluated. Methods and devices are disclosed in using a wavefront corrector to compensate for the aberration information provided by CG-WFS, in a combined imaging system, that can use one or more channels from the class of (i) optical coherence tomography (OCT), (ii) scanning laser ophthalmoscopy, (iii) microscopy, such as confocal or phase microscopy, (iv) multiphoton microscopy, such as harmonic generation and multiphoton absorption. In particular, a swept source (SS) is used that drives both an OCT channel and a coherence gated wavefront sensor, where:a) both channels operate according to SS-OCT principles;b) OCT channel integrates over at least one tuning scan of the swept source to provide a TD-OCT image of the object;c) CG-WFS integrates over at least one tuning scan of the swept source to provide an en-face TD-OCT mapping of the wavefront.For some implementations, simultaneous and dynamic aberration measurements / correction with the imaging process is achieved. The methods and devices for depth resolved aberrations disclosed, will find applications in wavefront sensing and adaptive optics imaging systems that are more tolerant to stray reflections from optical interfaces, such as reflections from the microscope objectives and cover slip in microscopy and when imaging the eye, the reflection from the cornea.

A scanning laser ophthalmoscope incorporates adaptive optics to compensate for wavefront aberrations in the eye. Light from a light source is scanned onto the retina. Light reflected from the retina is detected for imaging and is also used for wavefront sensing. The sensed wavefront aberrations are used to control an adaptive optic device, such as a deformable mirror, disposed in the path of the light from the source in order to compensate for the aberrations.

A combination of a confocal scanning laser ophthalmoscope and external laser sources is used for microphotocoagulation purposes. An opto-mechanical linkage device and beamsplitter is used to align the pivot point of the Maxwellian view of the scanning laser ophthalmoscope with the pivot point of non-scanning external laser beams. The same pivot point is necessary to minimize wavefront aberrations and to enable precise focussing of a therapeutic laser beam on the retina. An AOM and / or two-dimensional AOD can be inserted in the pathway of the Gaussian therapeutic beam to control intensity and spatial pattern of small and short-duration pulses. The location of the external laser beam on the retina is determined with the help of two synchronized detectors and image processing. One detector is used to localize moving fiducial landmarks of the retina. A second detector is used to locate on the retina the external laser aiming beam. Two different confocal apertures are used. Polarizing the aiming beam is necessary to further reduce unwanted reflections from the anterior corneal surface.

A portable MEMS-based scanning laser ophthalmoscope (MSLO). In one example the MSLO includes a laser illumination sub-assembly that generates a laser illumination beam, a two-dimensional MEMS scan mirror configured to receive and scan the laser illumination beam over at least a portion of the retina of an eye to be imaged, an optical system configured to direct the laser illumination beam from the scan mirror into the eye to illuminate the retina, and a detector sub-assembly configured to intercept optical radiation reflected from the eye to generate an image of the retina. The optical system includes a polarized beamsplitter positioned between the scan minor and the eye and configured to direct the laser illumination beam to into the eye and to direct the optical radiation reflected from the eye to the detector sub-assembly.

A portable MEMS-based scanning laser ophthalmoscope (MSLO). In one example, the MSLO includes a laser illumination sub-assembly, a two-dimensional MEMS scanning mirror, a conic front objective, and a detector sub-assembly all disposed within a portable housing. A battery configured to provide power to components of the MSLO may also be included within the housing. In one example, the laser illumination sub-assembly includes at least one laser configured to generate in each of two orthogonal dimensions one or more illumination beams separated from one another by a predetermined angle of separation. The MEMS scanning minor and conic front objective are configured to produce a two-dimensional area of illumination from the illumination beam(s) in each dimension and to direct the illumination from the scanning minor to the eye to illuminate the retina.

An adaptive optics scanning laser opthalmoscopes is introduced to produce non-invasive views of the human retina. The use of dual deformable mirrors improved the dynamic range for correction of the wavefront aberrations compared with the use of the MEMS mirror alone, and improved the quality of the wavefront correction compared with the use of the bimorph mirror alone. The large-stroke bimorph deformable mirror improved the capability for axial sectioning with the confocal imaging system by providing an easier way to move the focus axially through different layers of the retina.

Methods and devices are disclosed for acquiring depth resolved aberration information using principles of low coherence interferometry and perform coherence gated wavefront sensing (CG-WFS). The wavefront aberrations is collected using spectral domain low coherence interferometry (SD-LCI) or time domain low coherence interferometry (TD-LCI) principles. When using SD-LCI, chromatic aberrations can also be evaluated. Methods and devices are disclosed in using a wavefront corrector to compensate for the aberration information provided by CG-WFS, in a combined imaging system, that can use one or more channels from the class of (i) optical coherence tomography (OCT), (ii) scanning laser ophthalmoscopy, (iii) microscopy, such as confocal or phase microscopy, (iv) multiphoton microscopy, such as harmonic generation and multiphoton absorption. For some implementations, simultaneous and dynamic aberration measurements / correction with the imaging process is achieved. The methods and devices disclosed can provide wavefront sensing in the presence of stray reflections from optical interfaces.

Provided is an actuator including a substrate, a movable portion provided so as to be movable with respect to the substrate, at least three elastic bodies for supporting the movable portion to the substrate in a displaceable manner, a movable comb electrode supported by the movable portion and extending in a direction parallel to a surface of the substrate, and a fixed comb electrode supported by the substrate and extending in the direction parallel to the surface of the substrate in which the movable comb electrode and the fixed comb electrode are arranged so as to be alternately engaged with each other with a distance, and each of all of the elastic bodies has a long axis that forms an angle of more than 90° and 180° or less with respect to at least one of the other elastic bodies.

An image processing apparatus includes an extraction unit configured to extract a structure of a tested eye from an OCT image obtained by optical coherence tomography, an extraction unit configured to extract a structure of the tested eye from an eyeground image obtained by a scanning laser ophthalmoscope or a fundus camera, a calculation unit configured to calculate a reliability degree of the extraction for each of the extracted structures, and a display control unit configured to display the extracted structures superimposed on a image of eyeground according to the calculated reliability.

An adaptive optics scanning laser ophthalmoscopes is introduced to produce non-invasive views of the human retina. The use of dual deformable mirrors improved the dynamic range for correction of the wavefront aberrations compared with the use of the MEMS mirror alone, and improved the quality of the wavefront correction compared with the use of the bimorph mirror alone. The large-stroke bimorph deformable mirror improved the capability for axial sectioning with the confocal imaging system by providing an easier way to move the focus axially through different layers of the retina.

The invention discloses a diabetic retinopathy classification method by using a super lightweight SqueezeNet network. The method comprises the following steps: preparing lots of SLO (Scanning Laser Ophthalmoscope) fundus photographs aiming at each type of diabetic retinopathy and performing preprocessing and data amplification; establishing a super lightweight SqueezeNet deep convolutional neuralnetwork containing a fire module; training the deep convolutional neural network based on the lots of fundus photographs, and enabling the final output value of the deep convolutional neural network to accord with the classification results of the fundus photographs; automatically carrying out disease classification by utilizing the trained deep convolutional neural network. According to the method disclosed by the invention, due to application of the lots of fundus photographs comprising diagnostic markers, operations of automatically learning needed features from a training case library andperforming classification judgment are realized by virtue of super lightweight deep learning network and a few parameters, and data features for judgment and deep convolutional neural network parameters are continuously corrected in the training process, so that the classification accuracy and reliability in realistic application scenarios can be greatly improved.

A scanning laser ophthalmoscope comprises: a laser source that emits a laser beam; an irradiation optical system that scans the laser beam over a fundus two-dimensionally; a photoreceptor optical system that receives reflection from the fundus by using a photoreceptor element; an image processor that obtains an image of the fundus based on an output signal from the photoreceptor element; a monitor; and a controller that causes the monitor to display the obtained fundus image, wherein the image processor comprises a subtractive processing circuit that performs time-subtractive processing on the output signal from the photoreceptor element in a state where the output signal is input as an analog signal, and forms the fundus image based on the signal subjected to the subtractive processing.

A method, controller, and medium to control an adaptive optics scanning laser ophthalmoscope. Receiving from the ophthalmoscope a plurality of wavefront elements. Each element may be associated with an area of a beam of light received from a fundus. Each element includes shape data. The shape data represents a shape of a wavefront in a area of the beam. Each element includes status data. The status data is a confidence indicator of ability of the shape data to represent the shape of the wavefront with a particular level of accuracy. Calculating control data based on the shape data in the wavefront data and local gain. The local gain includes local gain elements. Each local gain elements is adjusted based on status data. Using the control data to adjust a shape of an illumination wavefront of an illumination beam used to illuminate the fundus.

A scanning laser ophthalmoscope and a method of operating a scanning laser ophthalmoscope are disclosed. The scanning laser ophthalmoscope includes a light source, a reflective optical system, an x- and y-coordinate scanner, and a refractive lens. The reflective optical system is configured to direct light emitted from the light source through the refractive lens to a user's eye, and to direct light reflected from the user's eye through the refractive lens to the x- and y-coordinate scanner.

Provided is an actuator formed in a substrate including a handle layer, an elastic body layer, and an insulating layer, the actuator including a movable portion supported to a support portion by an elastic body, a movable comb electrode formed on the movable portion, a fixed comb electrode supported by the support portion, and electrode wirings connected to the respective comb electrodes in which the elastic body supports the movable portion such that the movable portion is displaceable in a direction perpendicular to the substrate in accordance with voltages applied to the comb electrodes; the comb electrodes are made up of the handle layer, and the elastic body is made up of the elastic body layer; and a handle layer separation groove is provided to electrically separate between the handle layers of the support portions supporting the comb electrodes, and a structure reinforcing portion is formed across the separation groove.

A scanning laser ophthalmoscope comprises a light source (LS) arranged to generate a beam of light; a deformable mirror relay (DM, SM1); a first scanning relay (VS, SM2); a second scanning relay (HS, SM3); a wavefront sensor (WFS); and a detector (APD). The deformable mirror relay comprises a deformable flat mirror (DM) arranged to compensate for distortions detected by the wavefront sensor (WFS). Each of the scanning relays comprises a flat scanning mirror (VS, HS) arranged to scan the beam across the eye of a subject. At least one of the relays has an entry focal plane and an exit focal plane and further comprises a spherical mirror arranged to reflect the beam from the entry focal plane onto the flat mirror and to reflect light from the flat mirror into the exit focal plane.

A scanning laser ophthalmoscope may include: a light source configured to emit laser light; a scanner configured to scan the laser light emitted from the light source two-dimensionally; a guide mirror configured to guide the laser light scanned by the scanner to a fundus of an eye of a subject; a guide mirror holder configured to hold the guide mirror in a predetermined positional relationship with the eye of the subject; a light receiver configured to receive reflected light of the laser light reflected on the fundus; and an image generator configured to generate a fundus image based on the reflected light received by the light receiver. The guide mirror may be disposed on a path connecting the scanner and the fundus of the eye of the subject, and disposed in front of the eye of the subject. The scanner may be disposed at the guide mirror holder.

A scanning laser ophthalmoscope for scanning the retina of an eye is provided, comprising: a light source emitting a beam of light, a scanning relay element, wherein the light source and the scanning relay element provide for transmission from a surface point source at the pupil point of the eye to the eye Two-dimensional scanning of the light beam of the retina, and a static aberration correcting element (30), wherein the static aberration correcting element is shaped to provide correction for the aberration of at least some of the scan relay elements, the static aberration correcting element in the ophthalmoscope The position of is chosen to provide correction for the misalignment of at least some of the scan relay elements, which maintains the transfer of the light beam from the surface point source at the pupil point of the eye to the retina of the eye. The invention also provides a deflection correction element and a method of determining the shape of the deflection correction element.