Thin optical system for surgical procedures

Abstract

The present disclosure relates generally to optical systems for surgical procedures, and more particularly to optical relay systems for visualization systems used during ophthalmic microsurgical procedures. The optical systems described herein provide improved ergonomics for surgeons because they facilitate low-profile microscope cameras that allow the surgeon to view through the camera to a display screen or other monitor positioned ergonomically favorably for the ophthalmic procedure. Such optical systems also provide improved performance because the total magnification of the optical head can be divided among multiple lens barrels, thereby producing high-resolution images that allow the surgeon to more clearly view the ophthalmic anatomy. Still further, such optical systems provide improved manufacturability, along with reduced weight and manufacturing costs, because the lens barrels can have a fixed focal length for use with digital magnification mechanisms.

Description

[Background technology]

[0001] Vitreoretinal and cataract surgeries are among the most commonly performed ophthalmic procedures. As the name suggests, vitreoretinal surgery is performed within the gel-like vitreous humor and on the light-sensing retinal surface within the relatively small eye cavity. Common conditions requiring vitreoretinal surgery include epiretinal membranes, vitreomacular separation, vitreomacular traction syndrome, diabetic traction retinal detachment, proliferative vitreoretinopathy (PVR), retinal detachment, macular hole, and various diseases requiring microinjection procedures for gene and cell therapy. Cataract surgery, on the other hand, involves removing the eye's cloudy lens and replacing it with a new artificial lens. There are two types of cataract surgery: phacoemulsification, in which the cloudy lens is broken down and then removed using ultrasound, and extracapsular surgery, in which the cloudy core of the lens is removed intact.

[0002] Traditionally, surgeons performing vitreoretinal and / or cataract surgery have utilized surgical microscope eyepieces that provide magnified and illuminated images of ophthalmic structures. More recently, head-up digital surgical visualization systems have replaced the use of such microscopes. Such visualization systems, which rely on high-resolution stereoscopic cameras to transmit images from the patient's eye to a head-up display screen for viewing by the surgeon, offer advantages over traditional microscopes, including better ergonomics for the surgeon, reduced phototoxicity, peripheral visualization, improved magnification, and reduced eye strain.

[0003] However, despite the many advantages of heads-up digital surgical visualization systems, current designs of the optical heads (i.e., the bodies that carry the optical components) used therewith are not optimized for ophthalmic surgery in terms of optics, ergonomics, and / or general use. For example, current optical heads of such systems are tall and bulky, thereby impeding surgical access to the patient's eye as well as obstructing the surgeon's and / or assistant's view of the heads-up display screen. Still further, the optics of such optical heads introduce numerous optical distortions when increasing magnification or changing the field of view and / or depth of field, thereby reducing the accuracy and precision of the ophthalmic surgical procedure. Summary of the Invention [Problem to be solved by the invention]

[0004] Therefore, there is a need in the art for improved optical systems for visualization systems used during ophthalmic surgical procedures. [Means for solving the problem]

[0005] FIELD OF THE DISCLOSURE Embodiments of the present disclosure relate generally to optical systems for surgical procedures, and more particularly to optical relay systems for visualization systems used during ophthalmic microsurgical procedures.

[0006] In certain embodiments, an optical system for a surgical camera is provided, the optical system including two stereoscopic channels, each having a first lens barrel with one or more first optical systems configured to generate images having a wide field of view (FOV), and a second lens barrel with one or more second optical systems configured to generate images having a narrow FOV, the optical load of each stereoscopic channel being split between the first and second lens barrels.

[0007] So that the above-mentioned features of the present disclosure can be understood in detail, a more particular description of the present disclosure briefly summarized above can be had by reference to embodiments, some of which are illustrated in the accompanying drawings. It should be noted, however, that the accompanying drawings illustrate only exemplary embodiments and therefore should not be considered as limiting the scope of the invention, as other equally effective embodiments are possible. [Brief explanation of the drawings]

[0008] [Figure 1] 1 is a perspective view of an exemplary ophthalmic facility for ophthalmic surgical procedures including a digital visualization system, in accordance with certain embodiments of the present disclosure. [Figure 2A] FIG. 1 is a simplified top perspective view of an exemplary optical head according to certain embodiments of the present disclosure. [Figure 2B] 2B is a bottom perspective view of components of the optical head of FIG. 2A in accordance with a specific embodiment of the present disclosure. [Figure 2C] 2B is another top perspective view of the components of the optical head of FIG. 2A in accordance with certain embodiments of the present disclosure. [Figure 2D] 2B is a front view of components of the optical head of FIG. 2A in accordance with a specific embodiment of the present disclosure. [Figure 2E] 2B is a side view of components of the optical head of FIG. 2A in accordance with certain embodiments of the present disclosure. [Figure 3A] 2A-2E are simplified cross-sectional front views of an exemplary optical module, such as the optical module of the optical head of FIGS. 2A-2E, according to certain embodiments of the present disclosure. [Figure 3B] FIG. 3B is a rear perspective view of the optical module of FIG. 3A in accordance with a specific embodiment of the present disclosure. [Figure 4A] 3B is a perspective side view of an exemplary tandem of lens barrels of the optical module of FIG. 3A in accordance with certain embodiments of the present disclosure. [Figure 4B] 3B is a perspective side view of another exemplary tandem of lens barrels of the optical module of FIG. 3A, in accordance with certain embodiments of the present disclosure. [Figure 5A]2A-2E are schematic cross-sectional side views of portions of an exemplary optical module, such as the optical module of the optical head of FIGS. 2A-2E, in accordance with certain embodiments of the present disclosure. [Figure 5B] 5B is a schematic plan view of an exemplary configuration of the optical module of FIG. 5A, in accordance with certain embodiments of the present disclosure. [Figure 5C] 5B is a schematic plan view of another exemplary configuration of the optical module of FIG. 5A, in accordance with certain embodiments of the present disclosure. [Figure 6A] 1A-1C are perspective views of exemplary configurations of multiple optical modules in an optical head for use during different types of ophthalmic procedures, according to certain embodiments of the present disclosure. [Figure 6B] FIG. 5B is a plan view of the exemplary optical head configuration of FIG. 5A in accordance with certain embodiments of the present disclosure. [Figure 7A] 1A-1C illustrate a patient's eye as viewed by the digital visualization system described herein at different magnification levels, in accordance with certain embodiments of the present disclosure. [Figure 7B] 2A-2E, with its optical module moved to a first position, in accordance with certain embodiments of the present disclosure. FIG. [Figure 7C] 7C is another schematic cross-sectional side view of the optical head of FIG. 7B with its optical module moved to a second position, in accordance with a specific embodiment of the present disclosure. DETAILED DESCRIPTION OF THE INVENTION

[0009] For ease of understanding, where possible, identical elements common to the figures are designated with the same reference numerals. It is contemplated that elements and features of one embodiment may be beneficially incorporated in other embodiments without further reference.

[0010] In the following description, details are set forth as examples to facilitate understanding of the disclosed subject matter. However, it should be apparent to those skilled in the art that the disclosed implementations are examples and do not encompass all possible implementations. Therefore, it should be understood that reference to the described examples is not intended to limit the scope of the present disclosure. Any changes and further modifications to the described devices, apparatuses, and methods, and any further applications of the principles of the present disclosure, as would normally occur to one skilled in the art to which the present disclosure pertains, are fully contemplated. In particular, it is fully contemplated that features, components, and / or steps described with respect to one implementation can be combined with features, components, and / or steps described with respect to other implementations of the present disclosure.

[0011] It should be noted that, as described herein, the distal end or distal portion of a component refers to the end or portion that is closer to the patient's body during use of that component, while the proximal end or proximal portion of a component refers to the end or portion that is farther away from the patient's body.

[0012] As used herein, the term "about" may refer to a + / - 10% variation from the nominal value. It is understood that such a variation may be included in any value provided herein.

[0013] The present disclosure relates to optical systems for surgical procedures, and more particularly to optical relay systems for visualization systems used during ophthalmic microsurgical procedures.

[0014] As discussed above, many current optical heads for heads-up digital surgical visualization systems are not optimized for ophthalmic surgery in terms of optical components, ergonomics, and / or general use. For example, such optical heads can be tall and bulky, thereby impeding surgical access to the patient's eye as well as obstructing the surgeon's and / or assistant's view of the heads-up display screen. Furthermore, the optics within such optical heads can introduce numerous optical distortions when increasing magnification or changing the field of view and / or depth of field, thereby reducing the accuracy and precision of the ophthalmic surgical procedure. The present disclosure addresses these and other shortcomings of many current designs by providing a robust, low-profile optical head for an ophthalmic 3D stereo microscope camera that facilitates improved ergonomics and visibility during ophthalmic surgical procedures.

[0015] In certain embodiments, the optical head includes an optical module having two stereoscopic channels with two lens barrels per channel (i.e., one lens barrel per channel in tandem), thus providing a total of four lens barrels. In other embodiments, the optical head includes two or more optical modules, each including two stereoscopic channels with two lens barrels each, thus providing a total of eight or more lens barrels. In such embodiments, each optical module may be optimized for performing a different ophthalmic surgical procedure, such as a cataract / anterior procedure or a retina / posterior procedure. For example, different optical modules may be optimized for different depths of field than others to enable more efficient viewing of anatomical structures at different depth levels along the optical axis of the microscope camera, and / or different optical modules may be optimized for different resolutions than others depending on the size of the anatomical structures desired to be viewed during the ophthalmic surgical procedure. In further embodiments, different optical modules may be configured to perform at different fields of view (e.g., magnification levels). In certain embodiments, different modules may also be coupled to or utilized with different optical filters.

[0016] In yet another embodiment, each stereo channel of the optical head may be included on a sub-module of the optical module. For example, in a particular embodiment, the optical module may include "left" and "right" sub-modules corresponding to the "left" and "right" stereo channels, respectively. During assembly of the optical head, each sub-module, and therefore each stereo channel, may be constructed and aligned separately relative to each other and to other components of the optical head, thereby facilitating more efficient alignment and assembly of the optical head.

[0017] In certain embodiments, the optical head further includes one or more coaxial illumination sources. The coaxial illumination sources may be attached to the optical modules of the optical head or other components of the optical head such that illumination light generated by the coaxial illumination sources is coaxially aligned with one or more optical axes of the optical modules. For example, a single coaxial illumination source may be attached to each sub-module of the optical module such that illumination light generated by the coaxial illumination sources is coaxially aligned with one or more optical axes of the lens barrels in each sub-module. Thus, in certain examples, two, three, four, or more optical and / or illumination axes of the optical head may be coaxially aligned.

[0018] In certain embodiments, each sub-module, and therefore each stereoscopic channel, of the optical head may be constructed and aligned separately with each other (and / or other components of the optical head) during assembly of the optical head. Individual assembly and alignment of each stereoscopic channel facilitates easier alignment and assembly of the entire optical head and alleviates some of the overall tolerance issues associated with assembling and aligning multiple stereoscopic channels together. In certain embodiments, individual assembly and alignment of a sub-module or stereoscopic channel includes assembly and alignment of one or more lens barrels with one or more coaxial illumination sources. Thus, in such embodiments, the lens barrel of each sub-module or stereoscopic channel may be assembled and aligned with the coaxial illumination source before being assembled and aligned with another sub-module or stereoscopic channel of the optical head, allowing for more efficient assembly of the entire optical head.

[0019] In certain embodiments, each lens barrel of the optical module includes a fixed focal length architecture and is configured to cooperate with digital zoom, thereby producing high-resolution images without the need for moving components (e.g., moving lenses). In such embodiments, one lens barrel in each stereoscopic channel may include a narrow field-of-view lens barrel, and the other lens barrel in each stereoscopic channel may include a wide field-of-view lens barrel. In certain other embodiments, each lens barrel of the optical module includes one or more adjustable or movable lenses to provide optical zoom functionality.

[0020] In certain embodiments, the two lens barrels in each volumetric channel are arranged in a side-by-side configuration. In certain other embodiments, the two lens barrels in each volumetric channel are arranged in a stacked configuration. Thus, each lens barrel can "see" or receive input from the same optical axis, thereby reducing or eliminating any distortions and / or other resulting complications, such as the need for compensation, that arise when lens barrels are aligned with different optical axes. In such embodiments, the received light can be split between the two lens barrels in each volumetric channel via beam splitters and mirrors, with the majority of the light being directed to the narrow-field-of-view lens barrel (e.g., the higher-magnification lens barrel) while the remainder of the light is directed to the wide-field-of-view lens barrel. In certain embodiments, each of the lens barrels can be configured with a relatively low f / # and a high numerical aperture (NA), thereby facilitating higher resolution and more efficient use of light, allowing for the utilization of lower illumination levels, thus reducing phototoxicity and improving patient safety.

[0021] As a result of these and other features, the optical systems described herein provide improved overall ergonomics compared to more conventional systems. More specifically, the optical systems described herein facilitate a low-profile microscope camera that allows surgeons of all physical sizes to more easily view a display screen or other monitor positioned above / around the optical head in an ergonomically advantageous position (e.g., along the surgeon's line of sight and perpendicular to the operating room floor).

[0022] Conventional surgical systems and equipment, including visualization systems used during ophthalmic microsurgical procedures, are typically designed for users of "average" size and / or build. Therefore, using such conventional systems and equipment may require surgeons with more extreme physical characteristics (e.g., height, etc.) to exert additional effort and / or greater strain, which can lead to chronic health problems (e.g., chronic neck and back pain) associated with repeated, prolonged use. For example, surgeons of "shorter" height may need to position themselves in unergonomic ways to look over / around more conventional microscope cameras, for example, to view one or more display screens of a visualization system during an ophthalmic surgical procedure. Because surgeons may often need to view such display screens for extended periods of time, they also need to remain in unergonomic positions, increasing the amount of physical strain on the surgeon's body. Thus, the optical system described herein addresses this problem and others by allowing surgeons with more extreme physical characteristics, as well as surgeons with more "average" dimensions, to more comfortably view monitors and other devices in the operating room with little or no obstruction from the surgical microscope camera.

[0023] Additionally, the optical systems described herein also offer improved performance compared to more conventional systems because, by dividing the total zoom among multiple lens barrels, they provide high-resolution images that allow surgeons to see the ophthalmic anatomy more clearly. Still further, the optical systems described herein offer improved manufacturability, with reduced weight and manufacturing costs, because fixed focal length lens barrels with no moving optics are not only easier to manufacture with a relatively low scrap rate, but are also more robust and resistant to vibration and misalignment. These and other advantages of the optical systems described herein are described in more detail below.

[0024] 1 illustrates a perspective view of an exemplary ophthalmic facility 100 for ophthalmic surgical procedures, in accordance with certain embodiments of the present disclosure. While described with reference to ophthalmic surgical procedures, those skilled in the art having the benefit of this disclosure will readily appreciate that the disclosed techniques may be applied to a variety of other fields, such as anatomical diagnosis, surgical procedures, etc.

[0025] In the example of FIG. 1 , the ophthalmology facility 100 includes a digital visualization system 102, a surgical console 104, and a head-up display 106. The digital visualization system 102 includes a surgical camera 108 positioned above a patient's head on a patient table 110. In certain embodiments, the surgical camera 108 may be a high dynamic range (HDR) microscope camera having resolution, image depth, clarity, and color contrast that enable high-quality three-dimensional (3D) images of the patient's anatomy, such as ophthalmic anatomy. The surgical camera 108 includes a body or optical head that includes multiple optical components (i.e., optics) for facilitating the relay and capture of 3D images of the patient's anatomy, which are described in further detail in FIGS. 2A-6B . The surgical camera 108 may be communicatively coupled (e.g., via a wired connection, a wireless connection, etc.) to one or more head-up displays 106, which may display a stereoscopic representation of the 3D images, thereby providing a surgeon, staff, or other observer with a perception of depth into the patient's ocular anatomy. The surgical camera 108 may also be used to increase magnification of the ocular anatomy, change the field of view, and the like.

[0026] The stereoscopic representation of the 3D image can be viewed on the head-up display 106 using stereo glasses worn by the surgeon or another observer (e.g., as an autostereogram, using Fresnel lenses, etc.). The stereoscopic representation of the 3D image displayed on the head-up display 106 allows the surgeon to perform a procedure on the patient's eye while in a more ergonomic position, such as while sitting in a chair 112, without bending over the microscope eyepieces and straining, for example, their neck. While conventional microscope camera designs are tall and bulky and may therefore block the surgeon's view of, for example, the head-up display 106 or other equipment in the operating room, the camera 108 described herein includes a low-profile design that allows the surgeon to look above / through the camera 108 to the head-up display 106, which can be positioned along the surgeon's line of sight.

[0027] The surgical console 104 includes a controller (not shown) and, in certain embodiments, a receiver (not shown) in communication with the controller. In certain embodiments, the controller may be configured to cause the surgical console 104 to perform tasks related to driving one or more devices within the ophthalmic facility 100, such as the digital visualization system 102 and the head-up display 106. Accordingly, the surgical console 104 may be communicatively coupled via the receiver (e.g., via a wired connection, a wireless connection, etc.) to other devices within the ophthalmic facility 100, such as the digital visualization system 102 (including the surgical camera 108), the head-up display 106, and / or one or more surgical probes, to perform various surgical procedures. In certain examples, the surgical console 104 may receive and / or send signals to and from the digital visualization system 102 to control parameters associated with the camera 108, such as increasing / decreasing magnification, changing the field of view (FOV), applying filters, switching between stereoscopic channels and / or modules, etc. The surgical console 104 may also send signals to the heads-up display 106 to control parameters related to image manipulation or playback, such as starting / stopping video recording. In certain embodiments, the heads-up display 106 may also receive information, such as surgical parameters, from the surgical console 104 and display such information on the heads-up display 106 along with a stereoscopic representation of the 3D image of the patient's eye.

[0028] Using the surgical console 104, a user may control the digital visualization system 102, as well as other devices within the ophthalmology facility 100. In certain embodiments, a user may control such devices within the ophthalmology facility 100 via adjustment of digital or physical knobs on the surgical console 104 or by actuating a foot pedal 105 or other similar control device communicatively coupled to the surgical console 104.

[0029] 2A-2F illustrate various views of an exemplary optical head 200 of a surgical camera, such as surgical camera 108 of FIG. 1, in accordance with certain embodiments of the present disclosure. Optical head 200 includes an ergonomic, low-profile (e.g., low height) design that allows surgeons of all physical sizes to see above / around optical head 200 to view display screens or other monitors / equipment within an operating room setting without additional effort or strain.

[0030] Referring now to FIG. 2A , a simplified top perspective view of an optical head 200 according to an embodiment described herein is shown. The optical head 200 includes an outer casing 201, shown in phantom in FIG. 2A to reveal the internal components of the optical head 200. The outer casing 201 houses and protects the internal components of the optical head 200 (e.g., the optical module, described below, etc.) from damage and external contamination, and may also provide fastening points for stabilizing such internal components therein. The outer casing 201 may generally be formed of any suitable surgical-grade material, including surgical polymers, thermoplastics, thermosets, and / or elastomers. For example, the outer casing 201 may include polycarbonate, polypropylene, polyethylene, polymethyl methacrylate, polyvinyl chloride, polyamide, acrylonitrile butadiene styrene (ABS), etc. In certain embodiments, the outer casing 201 includes one or more surgical-grade metallic materials, including aluminum, titanium, stainless steel, and other metal alloys.

[0031] The outer casing 201 couples at its bottom end to a base plate 202. The base plate 202 serves as a base or support for the internal components of the optical head 200 (as well as the outer casing 201), which may be rigidly or movably secured to the optical head 200. Additionally, the base plate 202 may include an opening 205 into which an insert 207 may be removably positioned. The insert 207 may include a window 203 that facilitates the vertical entry and exit of light into and from the optical head 200. Like the outer casing 201, the base plate 202 may be formed of any suitable rigid, surgical-grade material, including surgical-grade metallic materials such as aluminum, titanium, stainless steel, and other alloys. In certain embodiments, the base plate 202 comprises a surgical-grade polymer, thermoplastic, thermoset, and / or elastomer, such as those described above. To reduce or eliminate the possibility of visual obstruction of the surgeon's line of sight to a display screen and / or other equipment in the operating room during a surgical procedure, the base plate 202 and outer casing 201 together form a low-profile shape / configuration for the optical head 200. In the example of Figure 2A, the base plate 202 and outer casing 201 form a generally rectangular parallelepiped shape, although other shapes / configurations are contemplated.

[0032] Within outer casing 201 and secured to base plate 202 is optical module 210, which includes multiple optical systems (e.g., optical devices, not shown) for relaying and modulating input light within optical module 210 (e.g., light reflected back from the patient's eye) to one or more optical sensors 216 and 218. Optical sensors 216 and 218 then receive / capture the relayed input light (as an image) for display as a three-dimensional (3D) representation on a head-up display, e.g., head-up display 106. The optical systems within optical module 210 form at least two separate and independent stereoscopic channels (e.g., a "left" channel for the user's left eye and a "right" channel for the user's right eye, not shown) to facilitate the 3D representation of the relayed and captured images.

[0033] In the example of FIG. 2A , the optical head 200 includes a Greenough-type optical head, thus having optics that form two separate and independent optical axes 212 a and 212 b (together referred to hereinafter as optical axis 212) for each respective “left” or “right” stereo channel. While many conventional microscope cameras utilize common main objective (CMO)-type optical heads, such a style often results in a tall and bulky optical head that can block the surgeon's line of sight to a heads-up display, for example, during an ophthalmic procedure. Furthermore, CMO-type optical heads typically require more lenses, thus increasing the overall cost and complexity of the surgical camera. Therefore, utilizing a Greenough-type optical head 200, for example, for the digital visualization system 102, allows for a less obtrusive and more efficient design of the surgical camera 108.

[0034] In certain embodiments, as described above, the optics for each stereoscopic channel of optical head 200 may be included in a separate sub-module 260 or portion of optical module 210. For example, as shown in FIG. 2A , optical head 210 includes two sub-modules 260 a and 260 b (e.g., “left” and “right” sub-modules, hereinafter jointly referred to as sub-modules 260), each sub-module 260 including the optics for a different stereoscopic channel. Thus, the optics of each sub-module 260 a and 260 b form one of optical axes 212 a or 212 b, respectively.

[0035] 2A , optical head 200 also includes a first mirror beam splitter module 240 within outer casing 201 and secured to base plate 202. First mirror beam splitter module 240 facilitates the in-coupling of input light (e.g., light reflected back from a patient's eye) into optical module 210 and the out-coupling of any illumination light generated by a light source within optical head 200 toward the surgical site. First mirror beam splitter module 240 includes one or more mirrors and / or beam splitters 242 of any suitable configuration for redirecting input light that enters optical head 200 perpendicularly through window 203 in insert 207 into optical module 210. Thus, first mirror beam splitter module 240 may be positioned above / adjacent to window 203, which serves as an opening for optical head 200. Similarly, optical module 210 may include one or more windows 211 that allow input light to pass through to one or more optics of optical module 210 for further relaying and / or manipulation. In certain embodiments, first mirror beam splitter module 240 is configured to transmit, e.g., redirect, input light horizontally into optical module 210 at an angle between about 45 and about 135 degrees relative to the initial orientation of the input light.

[0036] The optical head 200 may further include one or more coaxial illumination sources 250 configured to generate and deliver illumination light for illuminating a surgical site, e.g., the internal structures of a patient's eye, during a surgical procedure. In the example of FIG. 2 , the optical head 200 includes two coaxial illumination sources 250A and 250B (collectively referred to hereinafter as coaxial illumination sources 250), each generating and delivering illumination light along a respective illumination axis 252A or 252B (collectively referred to hereinafter as illumination axis 252). Each illumination axis 252 is aligned coaxially with the optical axis of the optical module 210, with illumination axis 252a aligned with optical axis 212a and illumination axis 252b aligned with optical axis 212b. The alignment of the illumination axes 252 and the optical axes 212 facilitates optimal illumination, and therefore optimal brightness, of the image captured by the optical head 200.

[0037] In certain embodiments, the coaxial illumination sources 250 may be mounted or assembled within the optical head 200 in any suitable configuration to facilitate coaxial alignment of the illumination axis 252 with the optical axis 212. For example, the coaxial illumination sources 250 may be mounted directly to the optical module 210. In some examples, each coaxial illumination source 250 may be mounted to a sub-module 260 of the optical module 210. During assembly of the optical head 200, each optical axis 212 may be separately aligned with the illumination axis 252 before the optical axes 212 are aligned together. Thus, once each optical axis 212 is aligned with its respective illumination axis 252, the illumination axis 252 and the optical axis 212 may remain aligned during further downstream assembly of the optical head 200.

[0038] In certain embodiments, the coaxial illumination source 250 may be positioned outside the optical head 200, and the light generated thereby may be transmitted into the optical head 200 along the illumination axis 252 via a liquid light pipe, fiber optic cable, or the like.

[0039] In general, any suitable type of illumination source may be utilized for coaxial illumination source 250. For example, in certain embodiments, coaxial illumination source 250 includes light-emitting diodes (LEDs), such as white light LEDs, red-green-blue (RGB) light LEDs, etc. In certain embodiments, coaxial illumination source 250 includes an incandescent lamp, such as a halogen or tungsten-halogen lamp.

[0040] In addition to the coaxial illumination source 250, the optical head 200 may also include one or more oblique illumination sources 270. In the example of FIG. 2A , a single oblique illumination source 270 is shown positioned through an opening 209 in the insert 207, which may be adjacent to the window 203. The oblique illumination source 270 may generate and transmit additional illumination light 272 (shown in FIG. 2B ) for increasing illumination of the surgical site during a surgical procedure. In certain embodiments, the oblique illumination source 270 may be positioned / configured to generate and transmit illumination light 272 along one or more illumination axes (not shown) that are positioned at an angle to, and therefore not coaxially aligned with, the optical axis 212 of the optical module 210. This “oblique” angle of the illumination light 272 generated by the oblique illumination source 270 thus facilitates illumination of tissue surrounding the surgical site in addition to the surgical site itself. In general, the oblique illumination source 270 may include the same or a different type of illumination source as the coaxial illumination source 250.

[0041] Also shown in FIG. 2A is actuator 280 and its associated components (e.g., gears, rods, belts, etc.). As described in more detail below, actuator 280 can be utilized to actuate various components of optical head 200, such as optical module 210, and one or more filters or apertures in optical module 210. Actuator 280 can include any suitable controlled motion motor, such as a servo motor. In certain embodiments, actuator 280 includes a stepper motor, such as a permanent magnet (PM) stepper motor, a variable reluctance (VR) stepper motor, and a hybrid synchronous (HY) stepper motor. In such embodiments, the stepper motor can be controlled via full-step positioning rather than micro-step positioning to generate less heat. A micro-stepping motor may require a significant current to be sent to the motor to maintain the micro-step position (generating significant heat), while full-stepping the motor requires only enough current to keep its coils activated (generating less heat). Thus, a stepper motor can be micro-stepped for smoother and quieter operation during operation, but can be stopped at full steps to reduce heat generation. The reduced heat generation facilitates reduced movement of the optics within the optical head 200 during use, and therefore, the alignment of such optics may be better maintained. In general, the actuators 280 described herein may be controlled by a user, e.g., a surgeon or other medical personnel, via any suitable method or mechanism. For example, in certain embodiments, the actuators 280 may be controlled via a foot switch, voice command, or other mechanism used to control / toggle devices, functions, or parameters of a surgical console and / or surgical system.

[0042] FIG. 2B shows a bottom perspective view of the internal components of the optical head of FIG. 2A in accordance with certain embodiments of the present disclosure. In FIG. 2B, the base plate 202 has been removed for clarity. As shown, the optical module 210 is movably coupled to a rail 284, which may be secured to the base plate 202 of the optical head 200. Sliding of the optical module 210 along the rail 284 facilitates translational movement of the optical module 210 toward and / or away from the first mirror beam splitter module 240 within the optical head 200. This movement of the optical module 210 relative to the first mirror beam splitter module 240 allows for adjustment of the working distance of the optical head 200 and focusing of images captured by the optical module 210 during a surgical procedure, as will be described in more detail below with reference to FIGS. 7B and 7C . In certain embodiments, the optical module 210 is directly coupled to the rail 284. In other embodiments, the optical module 210 is indirectly coupled to the rail 284 via a platform 282 that is movably (e.g., slidably) coupled to the rail 284, to which the optical module 210 can be secured, for example, via bolting.

[0043] Translation of the optical module 210 along the rails 284 is driven by at least one actuator 280. In the example of FIG. 2B , actuator 280a is shown, which may include a stepper motor for driving the movement of the optical module 210 along the rails 284, thereby adjusting the working distance and / or focus of the optical head 200. Actuator 280a, like the other actuators 280, may be controlled via user input. For example, in certain embodiments, a surgeon or other medical personnel may control actuator 280a via a foot switch, voice command, or other suitable methods and mechanisms used to control / toggle devices, functions, or parameters of the surgical console and / or surgical system.

[0044] 2B further illustrates illumination light 272 generated by oblique illumination source 270. Oblique illumination source 270 may be positioned through or at least partially adjacent to opening 209 in insert 207, thereby permitting propagation of illumination light 272 from oblique illumination source 270 toward the surgical site (and out of optical head 200). Insert 207, which may be removably attached to base plate 202, further includes window 203 to facilitate transmission of light to and from optical module 210. Thus, insert 207, and more specifically window 203, is positioned below first mirror beam splitter module 240, which splits and / or redirects light between optical module 210 and window 203. In certain embodiments, window 203 includes wedge optics 206 to reduce the generation of optical ghosts and other artifacts in images generated by optical head 200. Window 203 may generally include one or more such wedge optics 206 (e.g., in a stacked configuration) for each optical axis 212 of optical module 210 that passes through window 203. In the example of FIG. 2B, at least two wedge optics 206 (one for each optical axis 212a and 212b) are shown arranged side-by-side. In certain embodiments, window 203 may further include a fixed filter, such as an infrared (IR) or laser light filter. For example, in certain embodiments, the fixed filter may include a coating on the optics of window 203.

[0045] 2A and 2B, opening 209 and window 203 are illustrated as features of insert 207, although in other examples opening 209 and window 203 may be formed directly in base plate 202 (instead of opening 205). However, utilizing insert 207 may facilitate easier access for repair and / or replacement of various components of optical head 200, including oblique illumination source 270 and / or wedge optics 206.

[0046] FIG. 2C shows another top perspective view of an optical head 200 according to a specific embodiment of the present disclosure, with the optical module 210 of the optical head 200 shown in cross section along plane "AA" of FIG. 2A to reveal the optics therein. As shown, the optical module 210 includes two separate and independent channels 204a and 204b (e.g., one for each user's eye, hereinafter jointly referred to as channels 204), which may be disposed within separate and independent sub-modules 260a or 260b of the optical module 210, respectively. Within each channel 204 are multiple lens barrels. In the example of FIG. 2C, two lens barrels 208 and 209 are shown within each channel 204, which operate in tandem to divide the optical workload for each corresponding channel 204, as described in more detail below with reference to FIG. 3A. Each lens barrel 208 or 209 includes multiple optics, such as lenses, for relaying and / or modulating input light entering optical module 209, for example, along optical axis 212a or 212b, to optical sensors 216 and 218, respectively. The input light is redirected to each lens barrel 208 or 209 via one or more second mirror beam splitter modules 262 disposed within optical module 210 and including beam splitter 266 and mirror 267. In certain embodiments in which optical module 210 includes sub-modules 260a and 260b, one or more second mirror beam splitter modules 262 may be disposed between sub-modules 260a and 260b within optical module 210. In certain embodiments, the second mirror beam splitter module 260 is configured to transmit, e.g., redirect, the input light horizontally to the lens barrel 208 or 209 at an angle of about 45 to about 135 degrees relative to the orientation of the input light transmitted by the first mirror beam splitter module 240.

[0047] 2D and 2E illustrate the coincident axes of the optical module 210 and the coaxial illumination source 250 in accordance with certain embodiments of the present disclosure. More specifically, FIG. 2D illustrates the coincident optical axis 212 and illumination axis 252 in a front view of the internal components of the optical head 200, while FIG. 2E illustrates these coincident axes in a side view of the optical head 200. As shown, the optical axis 212a of the optical module 210, formed by one of the two channels 204 of the optical module 210, coincides with the illumination axis 252a of the coaxial illumination source 250a. Meanwhile, the optical axis 212b of the optical module 210, formed by the other of the two channels 204 of the optical module 210, coincides with the illumination axis 252b of the coaxial illumination source 250b. Furthermore, each pair of coincident axes 212, 252 converge to form a focal point, as shown in FIG. 2D. The coincident nature of optical axis 212 and respective illumination axis 252 is facilitated by the relative orientation of channels 204 (e.g., sub-modules 260) of optical module 210 and coaxial illumination source 250, as well as the placement and orientation of first mirror beamsplitter module 240 and second mirror beamsplitter module 262, which cause axes 212 to converge toward one another. In Figures 2D and 2E, the coincident optical axis 212 and illumination axis 252 are shown adjacent to one another for clarity.

[0048] 3A shows a simplified cross-sectional side view of optical module 210 having its optical axis 212, according to certain embodiments of the present disclosure. As shown, input light 301 (e.g., light reflected back from a patient's eye) is transmitted toward optical module 210 along optical axes 212a and 212b (together optical axis 212) of two stereoscopic channels 204a and 204b (together channels 204) via first mirror beam splitter module 240, respectively. Again, each channel 204a and 204b may be included in a separate sub-module 260a or 260b of optical module 210, which are assembled and aligned with one another. Input light 301 is then optionally split and relayed by optics disposed adjacent to or within multiple lens barrels (e.g., two or more lens barrels) of each channel 204, before reaching multiple optical sensors 216 and 218 for capturing and displaying the light as a 3D representation on a head-up display, e.g., head-up display 106.

[0049] As shown, each channel 204a and 204b includes at least a first lens barrel 208a or 208b (collectively referred to hereinafter as the first lens barrel 208) and a second lens barrel 209a or 209b (collectively referred to hereinafter as the second lens barrel 209), respectively. The first lens barrel 208 and the second lens barrel 209 in each channel 204 function in tandem to decompose the optical workload of the corresponding channel 204 into a multiple optical system (e.g., lens) system for wide versus narrow field of view observation, facilitating, in certain embodiments, an overall fixed focal length system for the optical head 200 without moving the optical system. As a result of the division of the optical workload by the two barrels, a user, e.g., a surgeon, can instantly switch between the first lens barrel 208 and the second lens barrel 209 in each channel 204 to obtain different fields of view (e.g., wide versus narrow frames). Additionally, without moving the lens, the optical module 210 enables "instantaneous" zoom, requiring only milliseconds or less to zoom from one magnification to another via a digital mechanism. Furthermore, utilizing two barrels in tandem for each channel 204 enables a picture-in-picture view, where two different views can be observed by a user at once. Dividing the total number of optics for each channel between two barrels also makes the optical head 200 easier to manufacture, as the tolerances for the optics within the individual barrels can be looser (because all optics do not have to be located within the same barrel for a channel).

[0050] To facilitate division of the optical workload among the lens barrels, the input light 301 may be split and reflected by one or more beam splitters 266a or 266b (collectively referred to below as beam splitter 266) and one or more mirrors 267a or 267b (collectively referred to below as mirror 267) of the second mirror beam splitter module 262. In certain embodiments, the beam splitter 266 and / or the mirror 267 may include an optical prism or other suitable optical device having one or more reflective or partially reflective surfaces.

[0051] 3A, a single second mirror beam splitter module 262 is disposed between sub-modules 260a and 260b of optical module 210. The single second mirror beam splitter module 262 includes two sets of beam splitters 266a and 266b and two sets of mirrors 267a and 267b for directing input light 301 (transmitted along optical axes 212a and 212b) in opposite directions through lens barrel tandems 208a and 209a or 208b and 209b. In certain other embodiments, two or more second mirror beam splitter modules 262 may be utilized, with each second mirror beam splitter module 262 including a single set of beam splitters 266 and / or mirrors 267. However, in any configuration, the placement of the second mirror beam splitter module 262 facilitates coaxial alignment of the optical axes of the multiple lens barrels in each three-dimensional channel 204 to form the optical axis 212 of the optical module 210. When utilized with the coaxial illumination source 250, three or more optical axes (e.g., the optical axes of the two lens barrels 208, 209 in the three-dimensional channel 204 plus the optical axis of the coaxial illumination source 250) may also be aligned (i.e., coincident) by the optical head 200. Thus, the angle beam splitter 266 and / or mirror 267 of the second mirror beam splitter module 262 define the optical axis angle α of the Greenough-type system of the optical head 200. In certain embodiments, the angle α is between about 1° and about 20°, e.g., between about 1° and about 15°, e.g., between about 5° and about 10°. In certain embodiments, the angle α is about 5°.

[0052] In certain embodiments, first lens barrel 208 comprises a wide field of view lens barrel having multiple lenses and / or other optics 312 each configured to generate a wide field of view image of the patient's anatomy from input light 301 and project that image onto optical sensor 216a or 216b (collectively referred to hereinafter as optical sensors 216). In certain embodiments, second lens barrel 209 comprises a narrow field of view lens barrel having multiple lenses and / or other optics 314 each configured to generate a magnified, narrow field of view image of the patient's anatomy and project that image onto optical sensor 218a or 218b (collectively referred to hereinafter as optical sensors 218). In use, the surgeon can instantly switch between the wide field of view lens barrel and the narrow field of view lens barrel (e.g., switch between image capture by optical sensors 216 and 218), which are configured to provide a seamless transition between the wide field of view and the narrow field of view view of the patient's anatomy. In certain embodiments, the optics 312 of the wide field of view first lens barrel 208 may include a ris-thri-pism or other wedge-type optic located at the end of the first lens barrel 208 closest to the second mirror beam splitter module 262 (e.g., opposite the sensor 218), which may be different from the other optics in the lens barrel 209. Such a ris-thri-pism allows for alignment of the optical axis of the wide field of view first lens barrel 208 with the optical axis of the narrow field of view lens barrel 209. In such embodiments, the ris-thri-pism or other wedge-type optic is rotationally adjustable for "steering" the optical path therethrough (into the lens barrel 209).

[0053] Optical sensors 216 and 218 may include any suitable type of imaging sensor. In certain embodiments, optical sensors 216 and 218 include ultra-high definition sensors with 4K or greater resolution. For example, in certain embodiments, optical sensors 216 and 218 include ultra-high definition sensors with 8K or greater resolution. In certain embodiments, optical sensors 216 and 218 include sensors rated at a resolution greater than or equal to twice the displayed (e.g., output) resolution. Utilizing sensors rated at twice the output resolution facilitates maintaining the very high resolution provided by the fixed focal length system of optical module 210 at all zoom levels up to 2x or 4x magnification.

[0054] As shown in FIG. 3A , in certain embodiments, the barrels within the channel 204 of the optical module 210 may be arranged in an opposing layout, i.e., the first lens barrel 208a of channel 204a may be arranged opposite and in an inverse (but parallel) orientation to the first lens barrel 208b of channel 204b, and the second lens barrel 209a of channel 204a may be arranged opposite and in an inverse orientation to the second lens barrel 209b of channel 204b. Such an opposing layout of the lens barrels allows for a compact, robust, and easily manufacturable design. For example, the opposing layout of the optical module 210 facilitates improved thermal performance of the optical head 200, and thus the surgical camera 108, during thermal fluctuations because the opposing lens barrels move in tandem, thus maintaining their coaxial arrangement. In more traditional microscope camera designs, such as CMO-style microscope cameras, the optical systems are typically arranged side-by-side. When these cameras heat up during use, the heat can cause the optics to move, typically shifting away from one another, thereby causing misalignment of the optics and distorting any 3D images collected therefrom. However, the opposed layout of the optics module 210 can reduce and / or eliminate misalignment of the optics due to heat loads.

[0055] In certain embodiments, first lens barrel 208 and second lens barrel 209 are designed to have a low f / # to facilitate higher resolution and more efficient use of light. More efficient use of light by the lens barrels allows for the utilization of lower illumination levels at the patient's eye, thereby reducing the harmfulness of light to the patient's eye. In certain embodiments, first lens barrel 208 and second lens barrel 209 may have an f / # of about f / 8, f / 6, f / 5, f / 4, f / 3, f / 2, etc. In certain embodiments, first lens barrel 208 and second lens barrel 209 have an f / # of about f / 8 to about f / 4. In some examples, an f / # lower than f / 4 may result in a large and unergonomic optical system, while an f / # lower than f / 8 may result in poor image resolution.

[0056] As described above, to facilitate tandem operation of the first lens barrel 208 and the second lens barrel 209 in each channel 204, the input light 301 is split and / or reflected by the beam splitter 266 and mirror 267 of the second mirror beam splitter module 262 into corresponding tandems in each channel. In certain embodiments, the input light 301 is split approximately 50:50 between the first lens barrel 208 and the second lens barrel 209 in each channel; in certain embodiments, the input light 301 is split approximately 60:40 between the first lens barrel 208 and the second lens barrel 209 in each channel 204, or vice versa; in certain embodiments, the input light 301 is split approximately 65:35 between the first lens barrel 208 and the second lens barrel 209 in each channel 204, or vice versa; in certain embodiments, the input light 301 is split approximately 70:30 between the first lens barrel 208 and the second lens barrel 209 in each channel 204, or vice versa; In certain embodiments, the input light 301 is split approximately 75:25 between the first lens barrel 208 and the second lens barrel 209, or vice versa, in each channel 204; in certain embodiments, the input light 301 is split approximately 80:20 between the first lens barrel 208 and the second lens barrel 209, or vice versa, in each channel 204; in certain embodiments, the input light 301 is split approximately 85:15 between the first lens barrel 208 and the second lens barrel 209, or vice versa, in each channel 204; in certain embodiments, the input light 301 is split approximately 90:10 between the first lens barrel 208 and the second lens barrel 209, or vice versa, in each channel 204; or in certain embodiments, the input light 301 is split approximately 95:5 between the first lens barrel 208 and the second lens barrel 209, or vice versa, in each channel 204.In certain embodiments, a majority of the input light 301 is reflected to a corresponding second lens barrel 209, e.g., a narrow field of view lens barrel, because the narrow field of view lens barrel has a higher magnification and many, if not most, ophthalmic surgical procedures are performed while the surgeon is viewing the patient's anatomy at the higher magnification.

[0057] The optical module 210, and thus the digital visualization system 102, may include any suitable type of magnification / zoom mechanism for magnifying the images generated by the first lens barrel 208 and the second lens barrel 209. For example, in certain embodiments, the zoom / magnification of the first lens barrel 208 and the second lens barrel 209 may be controlled by a digital mechanism, e.g., a digital cropping and rescaling mechanism via software on the digital visualization system 102 or the surgical console 104, thus facilitating a smaller array (e.g., body) of each barrel without requiring any moving parts therein (e.g., movable optics 212 or 214). In such embodiments, the lens barrels 208 and 209 may include fixed focal length optics 312 or 314, thereby making such lens barrels easier to manufacture. In certain embodiments, the zoom / magnification of the first lens barrel 208 and the second lens barrel 209 may be controlled by a mechanical mechanism (i.e., an optical mechanism), thus facilitating better image resolution but requiring moving optics 312 or 314. In yet other embodiments, one of the lens barrel tandems may be configured for use with a digital zoom mechanism, while the other barrel may include a mechanical zoom mechanism. For example, first lens barrel 208 may include a digital zoom mechanism and second lens barrel 209 may include a mechanical zoom mechanism, thus providing optical module 210 with a "hybrid" zoom system.

[0058] Optical system 312 and / or optical system 314 may generally include any suitable type of optical component for relaying input light 301 to optical sensor 216 or 218. For example, optical system 312 and / or optical system 314 may include a relay lens, a focusing lens, a diffractive element, a beam splitter, and / or other types of optical relay devices. In certain embodiments, first lens barrel 208 and second lens barrel 209 may further include one or more irises, one or more filters, and / or other similar light modulation devices. In the example of FIG. 3A , each of first lens barrel 208 and second lens barrel 209 includes an iris 320, which facilitates control of the amount of light passing through the respective lens barrel and alters the depth of field during observation. The irises 320 may be opened / closed via actuation by one or more actuators 280, as described below with reference to FIG. 3B . Additionally, the optical module 210 further includes a filter block 322 for each channel 204, which includes one or more filters 324 (e.g., color filters, infrared filters, laser light filters, etc.) for each lens barrel of the channel. Similar to the iris 320, the filters 324 of the filter block 322 can be selected via translation, such as sliding the filter block 322 into and out of position, as driven by one or more actuators 280. In further embodiments, one or more fixed or movable filters can be mounted external to the optical module 210 within the optical head 200, for example, adjacent its window 211 (not shown). In certain embodiments, the external fixed filter can include a coating on the optics of the window 203, such as an IR filter coating on a proximal or distal surface of the optics of the window 203. In certain embodiments, the external fixed filter can include a laser filter mounted in the insert 207 and having dimensions defined by the window 203.

[0059] In certain embodiments, the optical module 210 further includes a conduit 330. The conduit 330 may include an opening, channel, or duct formed through the optical module 210 in which an OCT fiber optic probe, a laser ranging probe, an oblique illumination source, a fixed light source, or the like may be disposed for use during a surgical procedure. The conduit 330 may generally be disposed centrally within the optical module 210, e.g., between the channels 204. For example, in FIG. 3 , the central channel 330 is disposed between the set of beam splitters 266 and their mirrors 267 through the second mirror beam splitter module 262. However, in examples in which two (or more) second mirror beam splitter modules 262 are utilized, the central channel 330 may be disposed between such modules.

[0060] FIG. 3B illustrates a rear perspective view of an optical module 210 and an actuator 280 coupled thereto, according to certain embodiments of the present disclosure. As described above, the optical module 210 may include one or more movable irises 320 and one or more movable filters 324, each of which may be driven / actuated by one or more actuators 280. In certain embodiments, a single actuator 280 may drive a single iris 320 and / or a single filter 324. In certain embodiments, a single actuator 280 may drive two or more irises 320 and / or two or more filters 324 for efficiency and synchronization of lens barrels in different channels 204 within the optical module 210. For example, in FIG. 3B, two motors 280a and 280b are shown on the back of the optical module 210 for driving four irises 320a-d (shown in phantom). Motor 280a is indirectly coupled to one of the irises 320a or 320b in each of lens barrels 208a and 208b (shown in FIG. 3A) via a shaft 340 and direct drive or belt drive assemblies 342a and 342b (shown in FIG. 3B as direct drive assemblies). Each drive assembly 342 may include one or more gears 344 and / or belts (if belt-driven) coupled to the shaft 340 for powering the irises 320a or 320b. Similarly, motor 280b is indirectly coupled to one of the irises 320c or 320d in each of lens barrels 209a and 209b via a shaft 350 and a set of belts or direct drive assemblies 352a and 352b (shown in FIG. 3B as belt drive assemblies), each of which may include one or more gears 354 and / or belts 356 coupling the shaft 350 to the irises 320c, 320d. Thus, one motor 280a may drive both the "left" stereo channel and "right" stereo channel irises 320a, 320b in lens barrel 208 (e.g., wide field of view irises), while another motor 280b may drive both the "left" stereo channel and "right" stereo channel irises 320c, 320d in lens barrel 209 (e.g., narrow field of view irises).

[0061] FIG. 4A shows a perspective side view of an exemplary tandem of lens barrels of optical module 210 in a first configuration, according to certain embodiments of the present disclosure. In the example of FIG. 4A, a first lens barrel 408a and a second lens barrel 409a, which may represent the tandem of barrels 208 and 209 in either channel 204 of FIG. 3A, are stacked on top of each other. Here, the first lens barrel 408a, which includes a lens barrel with a wide field of view, is stacked on top of the second lens barrel 409a, which includes a lens barrel with a narrow field of view. In such a configuration, the first lens barrel 408a and the second lens barrel 409a are positioned along and receive input light from the same optical axis 412 of optical module 210, and thus optical head 200. Therefore, input light passing along optical path 412 must be split and / or reflected by one or more beam splitters 466 and mirrors 467 to facilitate directing light into each barrel and then onto optical sensors 416a, 418a. As a result, less light can be directed into each barrel, but arranging the tandem of barrels in a stacked configuration does not facilitate loss or change of perspective when switching between views of the first lens barrel 408a and the second lens barrel 409a.

[0062] 4B shows a perspective side view of another exemplary tandem of lens barrels of optical module 210 in a second configuration, according to certain embodiments of the present disclosure. In the example of FIG. 4B, first lens barrel 408b and second lens barrel 409b, which may represent the tandem of barrels 208 and 209 in either channel 204 of FIG. 3A, are arranged side-by-side. In such a configuration, because first lens barrel 408b and second lens barrel 409b are arranged along and receive input light from separate optical axes 412a and 412b of optical head 200, respectively, no light splitting is required to direct the input light into each barrel and then onto optical sensors 416b and 418b. Instead, mirror 467 may be utilized to simply reflect the input light into each barrel, respectively. However, because the barrels are positioned along different optical paths, switching the view between the first lens barrel 408b and the second lens barrel 409b causes a loss or change of perspective for a user viewing the head-up display.

[0063] FIG. 5A shows a schematic cross-sectional side view of optical head 200 including optical module 210, while FIGS. 5B and 5C schematically illustrate different exemplary orientations of optical systems within lens barrels 208 and 209 of optical module 210, according to certain embodiments of the present disclosure. For clarity, FIGS. 5A-5C are described together herein. As shown in FIG. 5A and described above, input light 501 is reflected from patient's eye 510 along optical axes 512a and 512b by first mirror beam splitter module 240 into optical module 210. Within optical module 210, input light 501 is then directed by second mirror beam splitter module 262 into barrels 208a, 208b and / or 209a, 208b. Thus, the angle of the mirror 267 and / or beam splitter 266 of the second mirror beam splitter module 262, in addition to the angle of the optical system 312 or 314 (shown in FIG. 3A) within the lens barrel 208 or 209, respectively, can result in the lens barrel having either an emulated "tilted" orientation, as shown in FIG. 5B, or an emulated "straight" orientation, as shown in FIG. 5C.

[0064] In the “tilted” orientation of FIG. 5B , the major axes of lens barrels 208 and 209, and therefore optics 312 and 314, are positioned at a 0-degree angle relative to optical axis 512 of input light 501 as transmitted into lens barrels 208 and / or 209 by second mirror beam splitter module 262. This emulates a more traditional microscope configuration in which optics for different stereo channels are positioned at non-zero angles relative to one another (e.g., the stereo channels are “tilted”). Such an orientation allows sensors 216 and 218 to be centrally aligned (e.g., “in-line”) with the major axes of their respective lens barrels 208 and 209, further enabling the use of more compact optics 312 and 314. In certain embodiments, the tilted configuration may cause optical distortion known as the “keystone effect” in images collected by optical sensors 216 and 218, although this distortion may be compensated for by software-based distortion correction.

[0065] 5C , the major axes of lens barrels 208 and 209, and therefore optics 312 and 314, are positioned at a non-zero angle relative to optical axis 512 of input light 501, as transmitted into lens barrels 208 and / or 209 by second mirror beam splitter module 262. This emulates a more traditional microscope configuration in which the optics for different stereo channels are positioned parallel to one another (e.g., the stereo channels are "straight"). Unlike tilted configurations, the straight configuration may not require compensation or correction for distortions such as keystone, but may be more complex to assemble and may require larger sized optics and offset sensors 216 and 218 (e.g., not aligned with the major axes of their respective lens barrels 208 and 209).

[0066] Figure 6A schematically illustrates a perspective view of another exemplary configuration 600 of the optical head 200 for use in multiple different types of ophthalmic procedures, according to certain embodiments of the present disclosure. Figure 6B illustrates a plan view of the exemplary configuration 600 of Figure 6A, according to certain embodiments of the present disclosure. Thus, Figures 6A and 6B are described together herein for clarity.

[0067] In general, the optical head 200 can be configured for use in multiple different types of surgical procedures, such as cataract procedures, retinal procedures, and other types of ophthalmic surgical procedures. In certain embodiments, the optical head 200 can include multiple groups of lens barrels within an optical module or multiple optical modules, with each group or optical module optimized for performing one or more different types of surgical procedures. In the exemplary configuration 600 shown in FIGS. 6A and 6B , the optical head 200 includes two optical modules 610 a and 610 b (collectively referred to below as modules 610), with each module 610 optimized for performing at least one different type of surgical procedure. For clarity, only the lens barrel of the optical module 610 is shown in FIGS. 6A and 6B . As shown, each module 610 includes two channels 204 a and 204 b, one for each eye, with each channel 204 including a first lens barrel 208 a or 208 b and a second lens barrel 209 a or 209 b operating in tandem as described above. Thus, the optical head 200 configuration 600 includes a total of eight lens barrels, although additional optical modules 610, and therefore additional lens barrels, may be utilized in other embodiments.

[0068] The optical modules 610 may be arranged in any suitable configuration and at any suitable orientation relative to one another. In the example of FIG. 6B , optical modules 610a and 610b are shown as being arranged in a side-by-side configuration and parallel orientation, although other arrangements and / or orientations are also contemplated. Before or during a surgical procedure, a user, e.g., a surgeon, may select or switch between each optical module 610 by selecting or adjusting a digital or physical knob on a surgical console, e.g., surgical console 104, a digital or physical knob on a digital visualization system, e.g., digital visualization system 100, or by actuating a foot pedal or similar mechanism. In response, a controller in communication with the surgical console and / or digital visualization system may switch views between the optical modules 610.

[0069] As discussed above, each optical module 610 in FIGS. 6A and 6B may be optimized for performing a different ophthalmic surgical procedure, e.g., a cataract / anterior procedure or a retina / posterior procedure. Accordingly, in certain embodiments, each optical module 610 may be configured to display a different depth of field as needed to view the desired ocular anatomical structure for different types of ophthalmic surgical procedures. In certain embodiments, each optical module 610 may be configured to display a different resolution depending on the size of the anatomical structure targeted during such a surgical procedure. In further embodiments, each optical module 610 may be configured to have a different field of view (e.g., magnification level) and / or include a different optical filter, such as the filter 324 described above.

[0070] In yet other embodiments, a single optical module 610 including two channels 204, with each channel 204 having a first lens barrel 208 and a second lens barrel 209 operating in tandem therein, may be optimized to perform two or more different types of procedures. In such embodiments, the single optical module 610 may be configured to operate within technical specifications, such as depth of field, resolution, magnification level, input light level, optical filters, etc., applicable to each of the two or more different types of procedures.

[0071] 7A illustrates a patient's eye 702 viewed on a three-dimensional (3D) digital visualization system at different magnification levels, according to certain embodiments of the present disclosure. As described above, a surgical camera of a 3D digital visualization system may include an optical head having multiple lens barrels, one for each of two stereoscopic channels, and the optical load of each channel may be divided among the multiple lens barrels. The example of FIG. 7A illustrates the separation of the optical load in an optical head including optical head 200 having two lens barrels, e.g., optical module 210, in each channel, as viewed by a user on a corresponding digital visualization system head-up display, e.g., head-up display 106 of digital visualization system 102.

[0072] As shown at the far left of FIG. 7A , an observation process 700 for viewing the ophthalmic anatomy of a patient's eye 702 may begin with a view 710 including a 3D wide field of view (FOV) with no relative magnification (e.g., the image is magnified to a desired “starting” level). View 710 may be provided by a first wide field of view lens barrel in each stereoscopic channel, such as lens barrel 208 or 408 described above. A user may then magnify or zoom in on eye 702 by a first increment (e.g., 2X) to arrive at view 720, for example, via user adjustment of a digital or physical knob on a surgical console in communication with the 3D digital visualization system or by actuating a foot pedal or other similar control device communicatively coupled to the surgical console. In the example of FIG. 7A , view 720 may represent the maximum magnification or zoom level of the first lens barrel. To transition to view 720, a magnification / zoom mechanism for the first lens barrel, such as a digital zoom mechanism or an optical zoom mechanism, may be triggered by user input, thereby magnifying the image provided by the first lens barrel.

[0073] Upon reaching the maximum magnification or zoom level of the first lens barrel, the optical head may transition to a second, narrow-field-of-view lens barrel in each channel, such as lens barrel 209 or 409 described above, to arrive at view 730. View 730 may represent the 3D narrow FOV as provided by the second lens barrel without magnification or zoom and may be substantially identical to view 720 provided by the first lens barrel at its maximum magnification or zoom, thereby making the transition “seamless.” To achieve such a seamless transition between the images provided by the two lens barrels, the 3D digital visualization system may crop and rescale the image provided by the first, wide-field-of-view lens barrel as its magnification is increased to substantially match the unmagnified image provided by the second, narrow-field-of-view lens barrel. Additionally, by utilizing digital gain and offset (e.g., digital mechanisms), in addition to iris control of the lens barrels, the light levels, color balance, and depth of field of the image are matched.

[0074] Returning to FIG. 7A , after transitioning to view 730, receiving further input from the user to magnify or zoom in on eye 702 triggers a magnification / zoom mechanism of the second lens barrel, such as a digital or optical zoom mechanism, to magnify the image provided by the second lens barrel to arrive at final view 740.

[0075] 7B and 7C show schematic cross-sectional side views of the optical head 200 of FIG. 2A at different stages of adjusting its working distance and / or focus during use, in accordance with certain embodiments of the present disclosure. As mentioned above, in certain embodiments, the working distance of the optical head 200 and / or the focus of an image captured by the optical module 210 may be adjusted by changing the position (e.g., distance) of the optical module 210 relative to the first mirror beam splitter module 240 within the optical head 200. In such embodiments, the optical module 210 is movably mounted on a rail 284 within the optical head 200 and may be translated laterally along the rail 284 to adjust the working distance and / or focus of the optical head 200 and the optical module 210.

[0076] To illustrate this concept, Figure 7B illustrates optical module 210 in a first position 750 relative to first mirror beam splitter module 240, with input light 701 traveling a distance Z between mirror or beam splitter 242 of first mirror beam splitter module 240 and a sensor (e.g., 216 or 218) of lens barrel 208 or 209. In Figure 7B, optical head 200 has a working distance of Y, which is a function of, among other things, the total distance traveled by input light 701 between patient's eye 702 and the sensor of lens barrel 208 or 209. In Figure 7C, optical module 210 is moved a distance X toward first mirror beam splitter module 240 to a second position 760. 7C , the travel distance of input light 701 between the same mirror or beam splitter 242 of first mirror beam splitter module 240 and the sensor of lens barrel 208 or 209 is reduced by distance X (ZX). Conversely, working distance Y is increased by distance X (Y+X). Thus, by laterally translating optical module 210 along rail 284 toward first mirror beam splitter module 240, the working distance of optical head 200 can be increased, and vice versa. Similarly, such translation of optical module 210 can be used to focus the image captured by optical module 210. This overall mechanism not only provides a simple means of adjusting the working distance and focusing of optical head 200 and optical module 210, but also helps maintain a relatively compact (e.g., low height or low profile) design of optical head 200. Additionally, by moving the entire optical module 210, and therefore all lens barrels and optics, together, any tolerance issues associated with individual optics / barrel movements are avoided and the same resolution can be maintained over different working distances.

[0077] In summary, certain embodiments of the present disclosure include improved optical heads for visualization systems, such as heads-up digital surgical visualization systems. The optical heads described herein are optimized for use during several different ophthalmic surgical procedures, which also facilitate improved ergonomics and visibility during ophthalmic procedures. Certain embodiments further provide optical heads with lens barrels that facilitate higher resolution and more efficient use of light, thereby improving patient safety. Such lens barrels may also be arranged in a configuration that reduces the occurrence of optical distortion. Thus, the optical systems described herein offer several advantages over conventional systems.

[0078] Although cataract surgery and retinal surgery are discussed as examples of surgeries that may benefit from the described embodiments, other surgeries may benefit from the advantages of the surgical devices and systems described herein as well.

[0079] While the foregoing relates to embodiments of the present disclosure, other and further embodiments of the present disclosure may be devised without departing from the basic scope thereof, which scope is determined by the following claims.

[0080] Illustrative Embodiments Embodiment 1: A surgical camera comprising: an outer casing; a base plate coupled to a lower end of the outer casing, the base plate including a window to facilitate light entering and exiting the surgical camera; and an optical module coupled to the base plate and disposed within the outer casing, the optical module including two stereoscopic channels, each stereoscopic channel including: a first lens barrel including one or more first optical systems, the first lens barrel configured to generate images having a wide field of view (FOV); a first sensor coupled to the first lens barrel for receiving the images having the wide FOV; a second lens barrel including one or more second optical systems, the second lens barrel configured to generate images having a narrow FOV, the optical load of each stereoscopic channel being split between the first lens barrel and the second lens barrel; and a second sensor coupled to the second lens barrel for receiving the images having the narrow FOV.

[0081] Embodiment 2: A surgical camera as described in embodiment 1, wherein one or more first optical systems of each first lens barrel include a fixed focal length.

[0082] Embodiment 3: A surgical camera as described in embodiment 2, wherein the optical module includes a digital zoom mechanism for magnifying the image generated by each first lens barrel.

[0083] Embodiment 4: A surgical camera as described in embodiment 1, wherein one or more second optical systems of each second lens barrel include a fixed focal length.

[0084] Embodiment 5: A surgical camera as described in embodiment 4, wherein the optical module includes a digital zoom mechanism for magnifying the image generated by each second lens barrel.

[0085] Embodiment 6: A surgical camera as described in embodiment 1, wherein one or more second optical systems of each second lens barrel include a fixed focal length.

[0086] Embodiment 7: A surgical camera as described in embodiment 6, wherein the optical module includes a digital zoom mechanism for magnifying images generated by the respective first and second lens barrels.

[0087] Embodiment 8: A surgical camera as described in embodiment 1, wherein one or more first optical systems of each first lens barrel include movable optical systems for providing optical zoom.

[0088] Embodiment 9: A surgical camera as described in embodiment 1, wherein one or more second optical systems of each second lens barrel include movable optical systems for providing optical zoom.

[0089] Embodiment 10: A surgical camera as described in embodiment 1, wherein the first lens barrel and the second lens barrel of each three-dimensional channel are arranged in a side-by-side configuration within the optical module, and each of the first lens barrel and the second lens barrel is arranged along a different optical axis of the optical module.

[0090] Embodiment 11: A surgical camera as described in embodiment 1, wherein the first lens barrel and the second lens barrel of each three-dimensional channel are arranged in a stacked configuration within the optical module, and the first lens barrel and the second lens barrel are arranged along the same optical axis of the optical module.

[0091] Embodiment 12: A surgical camera as described in embodiment 1, wherein the two stereoscopic channels are arranged in an opposing layout within the optical module such that the first lens barrel and the second lens barrel of one of the two stereoscopic channels are arranged opposite the first lens barrel and the second lens barrel of the other of the two stereoscopic channels and in an inverted but parallel orientation.

[0092] Embodiment 13: A surgical camera as described in embodiment 1, wherein the optical module further includes a mirror beam splitter module, and the input light is split between and directed to the first lens barrel and the second lens barrel of each stereoscopic channel via the mirror beam splitter module.

[0093] Embodiment 14: A surgical camera as described in embodiment 1, wherein the input light is split between the first and second lens barrels of each stereoscopic channel in a ratio of approximately 30:70.

[0094] Embodiment 15: A surgical camera according to embodiment 1, wherein each of the first lens barrels and each of the second lens barrels of the two stereoscopic channels has an f-number of about f / 8 to about f / 2.

[0095] Embodiment 16: A surgical camera as described in embodiment 1, further comprising a pair of coaxial illumination sources, each of the coaxial illumination sources having an illumination axis that coincides with the optical axis of at least one of the first lens barrel and the second lens barrel of each stereoscopic channel.

[0096] Embodiment 17: A surgical camera as described in embodiment 16, wherein the illumination axis of each coaxial illumination source coincides with the first optical axis of the first lens barrel in each stereoscopic channel and the second optical axis of the second lens barrel in each stereoscopic channel.

[0097] Embodiment 18: A surgical camera as described in embodiment 17, wherein the illumination axis, the first optical axis and the second optical axis are aligned by one or more mirror beam splitter modules of the surgical camera.

[0098] Embodiment 19: A surgical camera as described in embodiment 1, wherein the optical module further includes a rail fixed to the base plate that is movably coupled to the rail, and an actuator for driving lateral movement of the optical module along the rail.

[0099] Embodiment 20: A surgical camera as described in embodiment 19, wherein lateral movement of the optical module along the rail facilitates adjustment of the working distance of the surgical camera.

[0100] Embodiment 21: A surgical camera as described in embodiment 20, wherein lateral movement of the optical module along the rail facilitates adjustment of the focus of the surgical camera.

[0101] Embodiment 22: A surgical camera as described in embodiment 1, wherein each of the first lens barrel and the second lens barrel includes one or more irises.

[0102] Embodiment 23: A surgical camera as described in embodiment 22, wherein the opening and closing of the iris is driven by one or more motors.

[0103] Embodiment 24: A surgical camera as described in embodiment 23, wherein the irises of both first lens barrels are driven by a single motor.

[0104] Embodiment 25: A surgical camera as described in embodiment 24, wherein the irises of both second lens barrels are driven by a single motor.

[0105] Embodiment 26: A surgical camera as described in embodiment 1, wherein the optical module is arranged to emulate a linear orientation of the first lens barrel and the second lens barrel.

[0106] Embodiment 27: A surgical camera as described in embodiment 1, wherein the optical module is arranged to emulate an inclined orientation of the first lens barrel and the second lens barrel.

Claims

1. 1. An optical system for a surgical camera, comprising: Two stereo channels, each of which: a first lens barrel including one or more first optical systems, the first lens barrel configured to generate an image having a wide field of view (FOV); a second lens barrel including one or more second optical systems configured to generate an image having a narrow FOV, the optical load of each stereoscopic channel being divided between the first lens barrel and the second lens barrel; and Two stereo channels, including An optical system comprising:

2. The optical system of claim 1 , wherein the one or more first optical systems of each first lens barrel include a fixed focal length.

3. The optical system of claim 2 , including a digital zoom mechanism for magnifying the image produced by each first lens barrel.

4. The optical system of claim 1 , wherein the one or more second optical systems of each second lens barrel include a fixed focal length.

5. 5. The optical system of claim 4, including a digital zoom mechanism for magnifying the image produced by each second lens barrel.

6. The optical system of claim 1 , wherein the one or more second optical systems of each second lens barrel include a fixed focal length.

7. 7. The optical system of claim 6, including a digital zoom mechanism for magnifying the images produced by the respective first and second lens barrels.

8. The optical system of claim 1 , wherein the one or more first optics of each first lens barrel includes a movable optic for providing optical zoom.

9. The optical system of claim 1 , wherein the one or more second optics of each second lens barrel includes a movable optic for providing optical zoom.

10. 2. The optical system of claim 1, wherein the first lens barrel and the second lens barrel of each three-dimensional channel are arranged in a side-by-side configuration, and each of the first lens barrel and the second lens barrel is arranged along a different optical axis of the optical system.

11. 2. The optical system of claim 1, wherein the first lens barrel and the second lens barrel of each three-dimensional channel are arranged in a stacked configuration, and the first lens barrel and the second lens barrel are arranged along a same optical axis of the optical system.

12. 2. The optical system of claim 1, wherein the two stereoscopic channels are arranged in an opposing layout such that the first lens barrel and the second lens barrel of one of the two stereoscopic channels are arranged opposite and in an inverse but parallel orientation relative to the first lens barrel and the second lens barrel of the other of the two stereoscopic channels.

13. 10. The optical system of claim 1, wherein input light is split between and directed to the first and second lens barrels of each stereo channel via a beam splitter and a mirror.

14. 10. The optical system of claim 1, wherein input light is split in a ratio of approximately 30:70 between the first and second lens barrels of each stereo channel, respectively.

15. 10. The optical system of claim 1, wherein each first lens barrel and each second lens barrel of the two stereoscopic channels has an f-number between about f / 8 and about f / 2.

Images