Eye visualization using confocal MEMS scanning

Abstract

A visualization system for dynamically visualizing the eye includes a laser module operable to output a primary laser beam along the beam axis, and a beam splitter positioned on the beam axis and configured to direct a first beam portion along the beam axis and a second beam portion along a detection axis perpendicular to the beam axis. A microelectromechanical system (MEMS) scanner is positioned on the beam axis and configured to output a scanning laser along the visualization path in accordance with the first beam portion. An avalanche photodiode (APD) detector receives the second beam portion. A 4F correlator optics system has spatial filters positioned along the visualization path. To achieve stereoscopic parallax, an optional optical plane may be positioned between the eye and the 4F correlator optics system.

Description

[Technical Field]

[0001] Cross-reference of related applications This application claims priority to U.S. Provisional Patent Application No. 63 / 420,113 filed on 28 October 2022, U.S. Provisional Patent Application No. 63 / 488,071 filed on 2 March 2023, and U.S. Provisional Patent Application No. 63 / 506,704 filed on 7 June 2023, each of which is incorporated herein by reference in its entirety.

[0002] Introduction This disclosure relates to a visualization system and related methods for assisting physicians in visualizing the internal anatomical structures of a patient's eye. As understood in the art, various in-hospital ophthalmic procedures require the attending physician to illuminate and observe the retina, macula, and surrounding areas within the vitreous cavity of the eye. Thus, as used herein and in the art, the term “visualization” refers to a dynamic and interactive examination of the eye by a physician. The visualized anatomical structures are generally not subject to image capture and analysis during the examination, but are interpreted in real time by the physician. [Background technology]

[0003] The types of in-hospital visualization work intended herein are often assisted by analog slit-lamp biomicroscopes or indirect ophthalmoscopy. Analog slit-lamp biomicroscopes are typically used for high-magnification and small-field observation of the macula / optic nerve and peripheral retinal regions, as well as for observing media opacities. Binocular indirect ophthalmoscopy is often used to perform peripheral retinal examinations, for example, when evaluating retinal holes, tears, or detachments. Other typical examinations may be performed to evaluate conditions such as retinal traction, retinal detachment, lattice degeneration, neovascularization, hemorrhage, coagulation or "floaters," displaced natural or intraocular lenses, and intraocular foreign bodies.

[0004] Some of the countless challenges associated with the use of analog slit-lamp biomicroscopes and indirect ophthalmoscopy include reflections or glare from the patient's cornea and lens, as well as scattered light / glare from corneal edema, scarring, epithelial defects, previous refractive surgery, and other possible causes or origins. Physicians are also challenged by scattered light or glare from cataracts, posterior capsule opacity, and intraocular lenses, particularly multifocal and diffractive-extended depth-of-focus (EDOF) and implantable collamer lenses (ICLs). Other ocular conditions such as vitreous condensation, hemorrhage, inflammatory cells, protein deposition or concentration, and stellate vitreous dysplasia can also affect accurate visualization of the patient's eye's anatomical structure. [Overview of the project] [Problems that the invention aims to solve]

[0005] Disclosed herein are automated visualization systems and related methods for assisting physicians in performing photovitreoretinal visualization processes. This technological solution, which relies on a narrowband light source and microelectromechanical system (MEMS)-based confocal spot scanning, helps mitigate the various problems typically associated with scattered light. The disclosed visualization system also increases the signal-to-noise ratio (SNR) by approximately 15 decibels (dB) or more compared to existing in-hospital visualization systems of the type summarized above. Similarly, this solution improves the overall outcome of in-hospital visualization by eliminating problematic reflections from, for example, the cornea and lens, thereby providing a clearer and more accurate view of the anatomical structure of the eye. [Means for solving the problem]

[0006] In possible embodiments, the visualization system includes a laser module, a beam splitter, a MEMS scanner, an avalanche photodiode (APD) detector, and a 4F correlator optics system having a spatial filter positioned along the visualization path. The laser module outputs a primary laser beam along the beam axis. The beam splitter is positioned along the beam axis and configured to (i) direct a first beam portion of the primary laser beam along the beam axis and (ii) direct a second beam portion of the primary laser beam along the detection axis, which is perpendicular to the beam axis. A portion of the MEMS scanner is positioned on the beam axis and configured to output a scanning laser toward the eye along the visualization path, corresponding to the first beam portion of the primary laser beam. In this embodiment, the APD detector receives the second beam portion of the primary laser beam.

[0007] In one or more embodiments, an optical plane is positioned between the eye and the 4F correlator optics system. The optical plane has a vertical axis and is configured to vibrate around it at a calibrated frequency to achieve stereoscopic parallax. This occurs when a physician visualizes the eye in real time using the visualization system.

[0008] Other embodiments avoid the use of the aforementioned optical plane, characterized in that there is no optical plane in the visualization system. Instead, the laser module includes a pair of laser modules, the beam splitter includes a pair of beam splitters, the MEMS scanner includes a pair of MEMS scanners, and the APD detector includes a pair of APD detectors. In this alternative implementation, the visualization system includes one of the laser modules, beam splitters, MEMS scanners, and APD detectors for each of the two different observation channels.

[0009] Another embodiment of the visualization system includes a laser module, a beam splitter, a MEMS scanner, an APD detector, a 4F correlator optics system, an APD detector, a digital eyepiece, an optical plane, and an electronic control unit (ECU). The laser module in this embodiment is operable to output a primary laser beam along the beam axis and includes an array of red, green, and blue (RGB) light-emitting diodes (LEDs) and an infrared (IR) laser diode, and the laser module is selectively switchable between the RGB LED array and the IR laser diode. The beam splitter is positioned in the beam axis and is configured to (i) direct a first beam portion of the primary laser beam along the beam axis and (ii) direct a second beam portion of the primary laser beam along the detection axis, which is then positioned perpendicular to the beam axis.

[0010] In this implementation, the MEMS scanner is positioned on the beam axis and configured to output a scanning laser toward the eye along the visualization path, corresponding to a first beam portion of the primary laser beam. The APD detector is configured to receive a second beam portion of the primary laser beam. The 4F correlator optics system has a Fourier plane and a spatial filter positioned along the visualization path, the spatial filter including at least one pinhole located in the Fourier plane. The optical plane is positioned between the eye and the 4F correlator optics system and has a vertical axis, and the optical plane is configured to vibrate around it at a calibrated frequency, thereby achieving stereoscopic parallax. This occurs when a physician visualizes the eye using the visualization system. The ECU is operable to perform confocal spot scanning of the eye using the laser module, MEMS scanner, 4F correlator optics system, and APD detector.

[0011] Another aspect of the present disclosure includes a method for dynamically visualizing an eye, which includes using a laser module that outputs an RGB laser beam and an IR laser beam to output a primary laser beam along a beam axis. The method also includes directing, via a beam splitter, (i) a first beam portion of the primary laser beam along the beam axis and (ii) a second beam portion of the primary laser beam along a detection axis. In response to the first beam portion of the primary laser beam, the method further includes outputting a scanning laser toward the eye along a visualization path via a MEMS scanner and detecting the second beam portion of the primary laser beam via an APD detector.

[0012] In addition, the method includes directing the second beam portion of the primary laser beam along the detection axis through a 4F correlator optical system having a spatial filter disposed within the visualization path. Confocal spot scanning of the eye is performed via an ECU using the laser module, the MEMS scanner, the 4F correlator optical system, and the APD detector.

[0013] The above-described features and advantages of the present disclosure, as well as other possible features and advantages, will become apparent from the following detailed description of the best mode for carrying out the present disclosure when interpreted in connection with the accompanying drawings.

Brief Description of the Drawings

[0014] [Figure 1] FIG. 1 is a schematic diagram of an exemplary in-hospital visualization process dynamically performed using a visualization system configured as described in detail herein. [Figure 2] FIG. 2 is a schematic diagram of a possible embodiment of the visualization system shown in FIG. 1. [Figure 3A] FIG. 3A is a diagram of an embodiment of the visualization system of FIGS. 1 and 2 in the process of performing confocal spot scanning of a patient's eye. [Figure 3B] FIG. 3B is a diagram of an embodiment of the visualization system of FIGS. 1 and 2 in the process of performing confocal spot scanning of a patient's eye. [Figure 4] FIG. 4 is a flowchart illustrating a method for visualizing a patient's eye using the visualization system of FIGS. 1-3B.

DETAILED DESCRIPTION OF THE INVENTION

[0015] The above and other features of the present disclosure will become more fully apparent when the following description and the appended claims are read in conjunction with the accompanying drawings.

[0016] Embodiments of the present disclosure are described herein. However, it will be understood that the disclosed embodiments are merely exemplary and that other embodiments may take various alternative forms. The figures are not necessarily drawn to scale. Some features may be exaggerated or minimized to show details of particular components. Thus, the specific structural and functional details disclosed herein should not be construed as limiting, but rather should be interpreted merely as a representative basis for teaching one skilled in the art to variously employ the present disclosure. As will be understood by those skilled in the art, various features shown and described with reference to any one of the figures can be combined with features shown in one or more other figures to create embodiments not explicitly illustrated or described. Combinations of the illustrated features provide representative embodiments for typical applications. However, various combinations and modifications of the features consistent with the teachings of the present disclosure may also be desired for a particular application or implementation.

[0017] In the following explanation, certain terms may be used for reference purposes only and are therefore not intended to be limiting. For example, terms such as “up” and “down” refer to directions within the referenced drawings. Terms such as “front,” “rear,” “forward,” “backward,” “left,” “right,” “rear,” and “side” describe the orientation and / or position of a component or element within an arbitrary reference frame, which will become clear by referring to the text and related drawings describing the component or element being discussed. Furthermore, terms such as “first,” “second,” and “third” may be used to describe separate components. Such terms may include the terms specifically mentioned above, their derivatives, and terms with similar meanings.

[0018] As those skilled in the art will understand, vitreoretinal examination is a dynamic process performed with multiple degrees of freedom. During a typical visualization process, the physician constructs a three-dimensional "mental model" of the anatomical structure of the patient's inner eye. Accurate visualization relies heavily on the constantly changing viewpoint and focal plane. For example, in the case of the slit lamp summarized above, the physician often needs to operate a joystick with a rotating handle to focus on or avoid focusing on the anatomical structure of the target eye. The indirect ophthalmoscope in that respect relies heavily on the physician's head / neck position and orientation, the patient's eye rotation and head position, and the placement and angle adjustment of the focusing lens.

[0019] Vitreoretinal imaging is a volumetric rather than planar operation. This makes three-dimensional / binocular observation of the anatomical structures of the eye an essential practice. During the examination, the physician's visual cortex calculates the depth of field by aligning corresponding points from each eye located within a deliberately selected depth subset of the paired volumes, i.e., within the fusion region of the visual holopter or Panum. Visual noise / scatter / clutter in the near and far fields is attenuated outside the visual holopter. The paired volumes located anterior to posterior to the visual holopter are twice as numerous, but do not appear so to the physician. Therefore, the need to improve spatial perception remains in this art, even when the displayed anatomical structures are not properly focused. This solution is intended to provide such improved spatial perception and other associated benefits detailed below.

[0020] Referring to drawings where similar reference numbers point to similar components, Figure 1 shows an in-hospital examination 10 in which an ophthalmologist or another attending physician 12 visualizes the eye 140 of a patient 14. This operation is performed dynamically, i.e., in real time, with the help of an automated visualization system 15. Embodiments of the visualization system 15 are described in detail below with reference to Figures 2 and 3, and the relevant method 50 is shown in Figure 4. The accompanying benefit of the physician's 12 enhanced visualization ability arises herein from the use of confocal, micro-electromechanical sensor (MEMS) based spot scanning of the eye 140. The physician 12 may be assisted during this effort by a handheld lens 13 in some implementations, as is understood in the Art and as further shown in Figure 3.

[0021] Although schematically shown in Figure 1 for simplification and clarity, the automated visualization system 15 of this disclosure can be implemented in different form factors, including a separate, standalone device (not shown) such as a slit lamp (not shown) summarized above, or as a headset 150 worn by or fixed around the head 12H of a physician 12. Thus, the compact and lightweight packaging resulting from the components of the automated visualization system 15 facilitates various implementations within the scope of this disclosure.

[0022] Referring to Figure 2, an automated visualization system 15 in a possible embodiment includes one or more laser modules 16, a power supply 18, for example, a rechargeable battery or a belt-worn battery pack, a digital eyepiece 26, and a two-axis MEMS scanner 20, i.e., having two scanning axes nominally indicated by the label "XY". The automated visualization system 15 may also include an electronic control unit (ECU) 22 configured to control the movement, position, state, or other parameters of various components of the automated visualization system 15 during the ongoing execution of the in-hospital examination 10 shown in Figure 1.

[0023] The MEMS scanner 20 contemplated herein can optionally be embodied as a biaxial piezoelectric scanning device having a resonant horizontal axis ("high-speed axis") and a quasi-static vertical axis ("low-speed axis"). For example, the MEMS scanner 20 may have individually controllable rotating mirrors or prisms to provide the physician 12 in Figure 1 with a mechanically variable parallax angle. In other possible configurations, the MEMS scanner 20 may be implemented as an electromagnetic or electrostatic device. Electronic control signals (CC) 22 Using this, the ECU22 can operate to communicate with various components of the automated visualization system 15 as described above when performing a confocal spot scan of the eye 140.

[0024] With respect to the laser module 16 in Figure 2, this light-emitting component may include three or more laser diodes (LDs) that collectively form a color LED array 160. The laser module 16 may additionally include an infrared (IR) laser diode 260 in a possible configuration. P ) is emitted by the laser module 16, and optionally similarly along the beam path (A 16 The beam path (A 16 It is directed toward the beam splitter (BSP) 33 along the )

[0025] The beam splitter 33 located at this position outputs the primary laser beam (LLP The beam splitter 33 divides the reflected light (LL1 and LL2) from the eye 140 into first and second beam portions (LL1 and LL2). As part of the intended structure, the beam splitter 33 may be positioned adjacent to a focusing lens (FL) 32 configured to direct the second beam portion (LL2) through a pinhole (PH) 30 onto an avalanche photodiode (APD) detector 360. Part of the APD detector 360 communicates with the ECU 22 wirelessly or via a physical transmission conductor and thus provides sensory feedback signals (FB) to the ECU 22 as part of the ongoing visualization process. R ) is also directed to the APD detector 360 via the digital eyepiece 26 as part of the detection process for final observation by physician 12 in Figure 1.

[0026] Therefore, the beam splitter 33 in Figure 2 is positioned and mounted to direct the first beam portion (LL1) from the laser module 16 into the MEMS scanner 20. Subsequently, the MEMS scanner 20 scans the laser (LL1) as described below. S The first beam portion (LL1) is vibrated and directed within the 4F correlator optical system 28 as the scanning laser (LL1). Therefore, the ECU 22 vibrates and directs the first beam portion (LL1) within the 4F correlator optical system 28. S The system is configured to control the confocal spot scanning process of the eye 140 by controlling the output of the relevant components of the automated visualization system 15 and the figures shown.

[0027] In a possible configuration, the LED array 160 shown in Figure 2 may include a stereoscopic viewing device constructed from a red (R) laser diode 160R, a green (G) laser diode 160G, and a blue (B) laser diode 160B for generating white light. For this purpose, commercially available, very compact RGB laser modules, such as the Veglas® RGB laser module from ams OSRAM AG, can be used. Commercial options for the MEMS scanner 20 include, as an example, a MEMS-based laser scanning module from Microvision, Inc. of Redwood, Washington. Such RGB laser diode-based embodiments of the MEMS scanner 20 contemplated herein are very compact and have an excellent dynamic range.

[0028] In an optional embodiment, the laser module 16 in Figure 2 is selectively switchable between constituent color laser diodes 160R, 160G, and 160B and an IR laser diode 260. The LED array 160 may be implemented as a Fabry-Perot laser diode setup having a relatively narrow bandwidth spectrum and degrees of control over gain and feedback within the laser cavity. As will be understood by those skilled in the art, unlike visible light, near-infrared (NIR) light does not require a darkened room or pupil dilation, for example, due to reduced dilation. For children with photophobia and other patients, the NIR spectrum can be a useful alternative or complementary light source for direct observation during examination. In other embodiments, only NIR implementations may be used. Such a method may be simpler in terms of the required optics and eliminates the need for multiple mirrors / beam splitters, as will be understood in the art, but at the expense of additional electronic sensing and display capabilities.

[0029] The "RGB+IR" solution of the present invention can be used to replace an indirect or slit lamp light source with an IR laser diode 260 (approximately 820 nm) and a color LED array, i.e., white light, in a switchable configuration. That is, the physician 12 can turn the IR laser diode 260 on and off as needed, and the APD detector 360 has sufficient sensitivity to detect such light. However, since IR direct view confocal visualization is not possible, the IR-based implementations contemplated herein require a 4F correlator optical system 28 for true confocal capability, along with a laser module 16 and a digital eyepiece 26, or a variant thereof. In some implementations, the image from the IR illumination may be displayed as green (approximately 550 nm) on a black background.

[0030] The APD detector 360, schematically shown in Figure 2, is used herein in conjunction with the laser module 16 to provide spot scanning and confocal imaging capabilities within the scope of this disclosure while significantly eliminating scattered light. As will be understood by those skilled in the art, an APD is a particular type of photodiode that generates high internal gain by applying a reverse voltage. Thus, the high gain, sensitivity, and fast response time resulting from the APD detector 360 increase the SNR compared to other types of photodetectors and are useful for the switchable color IR technology described herein. Exemplary commercially available APD detectors 360 available herein include those supplied by Hamamatsu Photonics KK of Hamamatsu City, or Excelitas Technologies® Corporation of Waltham, Massachusetts, USA.

[0031] Referring further to Figure 1, in other possible implementations, the automated visualization system 15, together with the 4F correlator optics system 28, can replace analog observation using conventional eyepieces instead of using a digital eyepiece 26 and APD detector 360. Real-time in-hospital visualization by physician 12 in Figure 1 can be enhanced using a miniature stereo OLED display, e.g., a 2K AMOLED pair from eMagin Corporation at Hopewell Junction, New York, USA, or an equivalent application-appropriate OLED pair from Seeya Information Technology of Shanghai, China, in a non-limiting embodiment in which physician 12 wears a headset 150 fixed around his head 12H. The laser module 16 and the digital eyepiece 26 can be packaged together on a wearable device, for example, with the digital eyepiece 26 positioned within the headset 150 or between the eyes of physician 12 mounted on the headset 150.

[0032] Referring further to FIG. 2, a 4F correlator optical system 28 contemplated herein and understood in the general art of optical physics forms an optical relay using two optical lenses L1 and L2. The lenses L1 and L2 are disposed within a visualization path (VV) extending between the MEMS scanner 20 and the eye 140. An input plane P1 is located one focal length away from the first lens L1 / ahead of the first lens L1. An output plane P2 is located one focal length after the second lens L2, i.e., closer to the eye 140 than the first lens L1. A Fourier plane (PF) is located midway between the respective input plane P1 and output plane P2. Thus, the acronym "4F" refers to four corresponding single focal length distances of separation between the input plane P1 and the first lens L1, between the first lens L1 and the Fourier plane (PF), between the Fourier plane (FP) and the second lens L2, and between the second lens L2 and the output plane P2. One or more pinholes 300 can be used as part of the 4F correlator optical system 28 to form a spatial filter 301 on the Fourier plane (PF), and the spatial filter 301 is configured to remove scattered light within the automated visualization system 15.

[0033] As understood by those skilled in the art, a time-series RGB image is integrated by the human brain within the visual cortex of the brain, provided that the perceived frame rate of each color exceeds the critical flicker fusion rate of approximately 60 Hz per color, or approximately 180 Hz in total for RGB applications. As contemplated herein, and as enabled by the 4F correlator optical system 28 and the APD detector 360, confocal spot scanning can improve the SNR by approximately 15 dB, mainly by reducing scattered light as described above. However, confocal spot scanning also significantly reduces the depth of field perceived by the physician 12 in FIG. 1.

[0034] Thus, as part of the illustrated configuration, an optional liquid lens 37 can be disposed between the pinhole 30 and the APD detector 360. The ECU 22 in such an embodiment is a control signal (CC 22As part of the sine wave drive, the liquid lens 37 can be driven to increase the depth of field of the physician 12 with limited degrees of freedom in the stereoscopic, RGB laser diode spot, or slit scanning embodiments of the automated visualization system 15. The implementation of sine wave drive may help reduce speckle in the direct view, stereoscopic RGB laser diode spot, or slit scanning embodiments of the visualization system 15. Thus, for example, the liquid lens 37 from Optotune Switzerland, AG can provide a desirable depth of field and can be selectively driven through a large amplitude focal range typically in about 1-2 milliseconds (ms).

[0035] Furthermore, to improve visualization, optional circular polarizers 51 (see Figures 3A and 3B) can be placed in the visualization path (VV). For example, the use of circular polarizers 51 may help increase contrast and reduce glare and reflection. Circular polarizers 51 also prevent crosstalk between the left / right channels in the embodiment of Figure 3B. In such a dual-channel implementation, optional circular polarizers 51 may be used in both channels to help eliminate crosstalk between channels.

[0036] Although the ECU22 is schematically shown as a single box in Figure 2 for clarity and simplicity of explanation, the ECU22 may include one or more network devices, each having a central processing unit or other processor 23 and a sufficient amount of memory 24 containing non-temporary (e.g., tangible) media involved in providing data / instructions that can be read by the processor 23. The memory 24 can take many forms, including but not limited to non-volatile and volatile media. As can be understood, non-volatile media may include optical disks and / or magnetic disks or other persistent memory, while volatile media may include dynamic random access memory (DRAM), static RAM (SRAM), etc. Any or all of these may constitute the main memory of the ECU22. Input / output circuits may be used to facilitate connection and communication with various peripheral devices used during ophthalmic procedures. Other hardware commonly used in the art, but not shown, may be included as part of the ECU22, including, but not limited to, a local oscillator or high-speed clock, signal buffers, filters, etc. The connection may be provided via BLUETOOTH®, Wi-Fi, HDMI®, NFC, DISPLAY PORT, THUNDERBOLT, or the like.

[0037] Furthermore, referring to the visualization system 15 in Figure 2, the vertical axis (A 29 An optical plane 29 having ) can be used in one or more embodiments. As described below, alternative embodiments that avoid the use of the optical plane 29, such as the one shown in Figure 3B, can be implemented. The optional optical plane 29 in Figures 2 and 3A would be useful in embodiments where the laser module 16, pinhole 300, and APD detector 360 are shared components, i.e., a single-channel implementation.

[0038] When the optical plane 29 is driven by an actuator 290, such as a resonant movable magnet Garbo, a piezoelectric stack (piezoelectric actuator), or a vibratory actuating device suitable for other applications, its vertical axis (A 29It is configured to vibrate around (A) in one or more embodiments. The optical plane 29 in one or more embodiments is configured as a polished, flat reference plane, such as fused silica or another material suitable for the application. For example, in the intended structure of the visualization system 15, the optical plane 29 is configured to vibrate around the vertical axis (A) in the scanning / descan path of the MEMS scanner 20 in order to achieve stereoscopic parallax. 29 It is configured to vibrate on its vertical axis (A). That is, the optical plane 29 is configured to vibrate on its vertical axis (A). 29 When vibrating around the scanning laser (LL), the movement of the optical plane 29 provides the type of parallax shift necessary for proper stereoscopic observation by the physician 12 in Figure 1. For this purpose, the actuator 290 is configured to vibrate the optical plane 29 at a calibrated frequency when mounted on the optical plane 29, which, when used herein, must be greater than a total frame rate of about 60 Hz or 180 Hz per color for the illustrated RGB embodiment in Figure 2. Thus the scanning laser (LL S The light passes through the optical plane 29 and enters the eye 140 through its lens 140L, and then illuminates the posterior wall 45 of the eye 140 within a controlled scanning range 45R.

[0039] Referring briefly to Figure 3A, a typical embodiment of the automated visualization system 15 uses a single-channel architecture in which the APD detector 360, MEMS scanner 20, pinhole 30, laser module 16, and beam splitter 33 are shared as a single device. Although omitted for clarity, a Garbo-controlled mirror device may be controlled downstream of the beam splitter (BSP) 33 to provide the physician 12 with right and left channel observation capabilities. In this configuration, the automated visualization system 15 in Figure 3A places the aforementioned laser module 16 in close proximity to the beam splitter 33. In this particular embodiment, the beam splitter 33 controls the primary laser beam (LL P The primary beam path (A) is directed toward the MEMS scanner 20. In this configuration, the MEMS scanner 20 is directed toward the primary beam path (A) 16 A scanning laser (LL) is transmitted through a high-diopter handheld lens 13, which is positioned within and may interpose within the ) SThe scanning laser (LL) is then directed toward the eye 140. The term "high diopter" as used herein may vary depending on the specific examination being performed. For example, but not limited to, a high diopter handheld lens 13 may be a 78-90 diopter lens or a 20-30 diopter lens. The scanning laser (LL) is then directed toward the eye 140. S The light passes through the lens 140L of the eye 140 and illuminates the posterior wall 45 during the in-hospital examination 10 in Figure 1.

[0040] As an alternative to the structure in Figure 3A, the automated visualization system 15A in Figure 3B avoids the use of the optical plane 29 and (single) laser module 16 shown in Figures 2 and 3. Instead, the automated visualization system 15A uses an ECU 22 and electronic control signals (CC). 22 The right / left channel operation is adjusted by doubling the number of a particular component and using it in a separate observation channel. Channel switching can be achieved using a suitable commercially available micromechanical fiber optical switch, e.g., the LightBend® family of high-performance optical switches from Agiltron®, Inc. of Woburn, Massachusetts. As shown in the figure, this includes the integration of a separate pair / first and second laser modules 16A and 16B, first and second AVD detectors 360A and 360B, and first and second beam splitters 33A and 33B. Similarly, the architecture in Figure 3B requires two biaxial MEMS scanners 20A and 20B.

[0041] In the exemplary dual-channel implementation shown in Figure 3B, the ECU22 controls the electronic control signals (CC). 22 The operation of the APD detectors 360A and 360B, laser modules 16A and 16B, and MEMS scanners 20A and 20B are synchronized via the APD detectors 360A and 360B, and configured to rapidly alternate between the left and right channels. Such a technique avoids the need for the optical plane 29 and its associated actuators 290 described above. The setup in Figure 3B can help avoid undesirable crosstalk and the need for complex optical systems such as mirrors or prisms by arranging separate right / left channels for observation by the physician 12 in Figure 1.

[0042] Therefore, the laser module 16 in Figure 2 may include a pair of laser modules 16A and 16B, the beam splitter 33 may include a pair of beam splitters 33A and 33B, the MEMS scanner 20 may include a pair of MEMS scanners 20A and 20B, the APD detector 360 may include a pair of APD detectors 360A and 360B, and the visualization system 15A in Figure 3B may include one laser module 16A, 16B, beam splitters 33A, 33B, MEMS scanners 20A, 20B, and APD detectors 360A, 360B, respectively, for each of two different / left / right observation channels.

[0043] Referring to Figure 4, Method 50 can be performed via the ECU 22 in Figure 2 and its embodiments in Figures 3A and 3B when the physician 12 in Figure 1 dynamically visualizes the eye 140. For example, computer-readable instructions can be recorded in memory 24 in Figure 2 and executed by the processor 23 to cause the ECU 22 or other hardware components of the automated visualization system 15 to perform the described operation. Figure 4 is organized into separate logical blocks for simplification, each describing one or more corresponding functions performed in the process of performing Method 50.

[0044] In an exemplary embodiment, Method 50 uses the laser module 16 of Figures 2 and 3A, or via the dual laser modules 16A and 16B of Figure 3C, to control the beam axis (A 16 ) along the primary laser beam (LL P Block B52 ("LL") includes outputting ) p The operation begins with ''). In one or more implementations, this operation can instruct the laser module 16 or 16A, 16B to output the primary laser beam as a red, green, blue (RGB) laser beam and / or an infrared (IR) laser beam. The method then proceeds to block B54.

[0045] Block B54 ("LL PThe primary laser beam (LL) is split through the beam splitter 33 in Figures 2 and 3A (or the dual beam splitter 33A and 33B in Figure 3B). P The beam is divided into its constituent first and second beam sections (LL1, LL2), and then the first beam section (LL1) is divided along the beam axis (A 16 This includes directing along the detection axis (A). Next, the second beam portion (LL2) is directed along the detection axis (A). 360 It is oriented toward the APD detector 360 (or dual APD detectors 360A, 360B) along the line. Method 50 then proceeds to block B56.

[0046] Block B56 ("Output LL") S In "), the primary laser beam (LL P In response to the first beam portion (LL1) of the laser, the MEMS scanner 20 (or the dual MEMS scanners 20A and 20B in Figure 3B) scans the laser (LL1) along the scanning axis, i.e., the visualization path (AA). S ) outputs. Next, method 50 proceeds to block B58.

[0047] In block B58 ("Photodetection"), the APD detector 360 detects the primary laser beam (LL P It is used to detect the second beam portion (LL2) of the APD. Similarly, the embodiment according to the setup in Figure 3B uses dual APD detectors 360A, 360B for this purpose. Method 50 then proceeds to block B60 as the APD detectors 360, 360A, or 360B output a feedback signal (FB) to the ECU 22, and the feedback signal (FB) indicates the second beam portion (LL2).

[0048] Block B60 ("4F") is the primary laser beam (LL P This involves directing the second beam portion (LL2) of ) through the 4F correlator optical system 28 along the visualization path (AA), the latter having the spatial filter 301 shown in Figure 2. The method then proceeds to block B62.

[0049] In block B62 ("Vibrating the optical plane"), method 50 in the embodiment using the optical plane 29 in Figures 2 and 3A involves vibrating the optical plane 29 about its vertical axis (A 29 This includes ) which is done at a calibrated frequency of at least about 60 Hz / color, or a total of 180 Hz as described above, and is used to achieve stereoparallax when the physician 12 in Figure 1 visualizes the eye 140 using the automated visualization system 15 described herein. As described above, the embodiment in Figure 3B avoids the use of the optical plane 29. Therefore, method 50 using the architecture of Figure 3B does not perform block B62. Method 50 then proceeds to block B64.

[0050] Block B64 ("Confocal Spot Scanning") includes performing a confocal spot scan of the eye 140 in Figures 1-3 via the ECU 22 using the laser module 16, 16A, or 16B, the MEMS scanner 20, 20A, or 20B, the 4F correlator optical system 28, the APD detector 360, 360A, or 360B, and, in the case of Figures 2 and 3A, the optical plane 29. This may include driving an optional liquid lens 37 via the ECU 22 to increase the depth of field of the physician 12 using a sine wave, and / or using an optional circular polarizer 51 in the visualization path (VV) in Figure 3 to increase contrast and reduce glare and reflections.

[0051] The aforementioned disclosure enables the construction of an indirect ophthalmoscope for digital electronic observation of a patient's eye 140 in a hospital setting. Typical techniques allow for optional switching between RGB and IR illumination and observation via a digital eyepiece 26 as shown in Figure 2. One of the advantages of this technique is the better visualization made possible by the confocal laser diode-based scanning described above. This benefit is widely observed in the presence of corneal edema or scarring cataracts, intraocular lenses (IOLs), particularly multifocal IOLs, posterior capsule opacity, and vitreous haze or hemorrhage (all of which are common sources of light scattering). These are only some of the incidental advantages of the above solution, as will be understood by those skilled in the art in light of the aforementioned disclosure.

[0052] While detailed descriptions and drawings support and illustrate this disclosure, the scope of this disclosure is defined solely by the claims. Although several best modes and other embodiments for carrying out the disclosure described in the claims have been described in detail, various alternative designs and embodiments exist for carrying out the disclosure defined in the attached claims.

[0053] Furthermore, the features of the embodiments shown in the drawings or the various embodiments referred to herein should not necessarily be understood as independent embodiments. Rather, each of the characteristics described in one example of an embodiment can be combined with one or more other desirable characteristics from other embodiments, resulting in other embodiments that are not described in words or not described by reference to the drawings. Accordingly, such other embodiments are included within the framework of the appended claims.

Claims

1. A visualization system for dynamically visualizing the eye, A laser module capable of operating to output a primary laser beam along the beam axis, A beam splitter is positioned along the beam axis and configured to (i) direct a first beam portion of the primary laser beam along the beam axis, and (ii) direct a second beam portion of the primary laser beam along the detection axis, wherein the detection axis is perpendicular to the beam axis and the beam splitter is located A microelectromechanical system (MEMS) scanner is positioned on the beam axis and configured to output a scanning laser toward the eye along a visualization path according to the first beam portion of the primary laser beam, An avalanche photodiode (APD) detector configured to receive the second beam portion of the primary laser beam, A 4F correlator optical system having spatial filters arranged along the visualization path, A visualization system equipped with [a specific feature].

2. The visualization system according to claim 1, further comprising an optical plane positioned between the eye and the 4F correlator optical system, the optical plane having a vertical axis configured to vibrate around it at a calibrated frequency, thereby achieving stereoscopic parallax when a physician visualizes the eye in real time using the visualization system.

3. The visualization system according to claim 1, wherein the laser module includes a pair of laser modules, the beam splitter includes a pair of beam splitters, the MEMS scanner includes a pair of MEMS scanners, and the APD detector includes a pair of APD detectors, thereby the visualization system includes one of the laser modules, the beam splitter, the MEMS scanner, and the APD detector in each of two different observation channels.

4. The visualization system according to claim 3, further comprising a lens that can be selectively positioned within the visualization path between the optical plane and the eye.

5. The visualization system according to claim 1, wherein the laser module includes an array of red, green, and blue (RGB) light-emitting diodes (LEDs).

6. The visualization system according to claim 5, wherein the laser module includes an infrared (IR) laser diode that can selectively switch between an RGB laser beam from the LED array and an IR laser beam from the IR laser diode.

7. The visualization system according to claim 1, further comprising the laser module, the MEMS scanner, the 4F correlator optical system, and an electronic control unit (ECU) capable of performing confocal spot scanning of the eye using the APD detector.

8. The visualization system according to claim 7, further comprising a liquid lens that is operable to increase the depth of field of a physician when using the visualization system, the liquid lens being sinusoidally driven by the ECU.

9. The visualization system according to claim 1, further comprising an organic light-emitting diode (OLED) digital eyepiece.

10. The visualization system according to claim 1, further comprising a headset configured to be worn by a physician when dynamically visualizing the eye, wherein the visualization system is attached to the headset.

11. The visualization system according to claim 1, wherein the 4F correlator optical system includes a Fourier plane, and the spatial filter includes at least one pinhole located in the Fourier plane.

12. The visualization system according to claim 1, further comprising circular polarizers arranged along the visualization path.

13. A visualization system for dynamically visualizing the eye, A laser module capable of emitting a primary laser beam along a beam axis, wherein the laser module includes an array of red, green, and blue (RGB) light-emitting diodes (LEDs) and an infrared (IR) laser diode, and the laser module is selectively switchable between the RGB LED array and the IR laser diode. A beam splitter arranged on the beam axis, wherein (i) the first beam portion of the primary laser beam is along the beam axis, and (ii) the second beam portion of the primary laser beam is along the detection axis (A ３６０ The detection axis is configured to be directed along the beam axis, and the detection axis is arranged perpendicular to the beam axis, with a beam splitter and A microelectromechanical system (MEMS) scanner is positioned on the beam axis and configured to output a scanning laser toward the eye along a visualization path according to the first beam portion of the primary laser beam, An avalanche photodiode (APD) detector configured to receive the second beam portion of the primary laser beam, A 4F correlator optical system having a Fourier plane and spatial filters arranged along the visualization path, wherein the spatial filters include at least one pinhole located on the Fourier plane, Digital eyepiece and An optical plane positioned between the eye and the 4F correlator optical system, having a vertical axis, the optical plane vibrating at a calibrated frequency around the axis, thereby achieving stereoscopic parallax when a physician visualizes the eye using the visualization system; An electronic control unit (ECU) capable of operating to perform confocal spot scanning of the eye using the laser module, the MEMS scanner, the 4F correlator optics system, and the APD detector. A visualization system equipped with [a specific feature].

14. The visualization system according to claim 12, wherein the optical plane includes one or more piezoelectric actuators.

15. The visualization system according to claim 12, further comprising a liquid lens that is operable to increase the depth of field of a physician when visualizing the eye, wherein the liquid lens is sinusoidally driven by the ECU.

16. The visualization system according to claim 12, further comprising circular polarizers arranged along the visualization path.

17. The visualization system according to claim 12, further comprising a headset configured to be worn by a physician when dynamically visualizing the eye, wherein the visualization system is attached to the headset.

18. A method for dynamically visualizing the eyes, Using a laser module that outputs red, green, and blue (RGB) laser beams and infrared (IR) laser beams, a primary laser beam is output along the beam axis. (i) the first beam portion of the primary laser beam is directed along the beam axis, and (ii) the second beam portion of the primary laser beam is directed along the detection axis via a beam splitter. Depending on the first beam portion of the primary laser beam, a scanning laser is output towards the eye along the visualization path via a micro-electromechanical system (MEMS) scanner. The second beam portion of the primary laser beam is detected via an avalanche photodiode (APD) detector, The second beam portion of the primary laser beam is directed through a 4F correlator optical system having a spatial filter positioned along the detection axis and within the visualization path. Using the laser module, the MEMS scanner, the 4F correlator optical system, and the APD detector, confocal spot scanning of the eye is performed via an electronic control unit (ECU). Methods that include...

19. The method according to claim 18, further comprising using a sine wave to drive a liquid lens via the ECU, thereby increasing the physician's depth of field when dynamically visualizing the eye.

20. The method according to claim 18, further comprising vibrating the optical plane around the vertical axis of the optical plane at a calibrated frequency, thereby achieving stereoscopic parallax when a physician dynamically visualizes the eye.

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