Anatomically, the human eye is divided into two distinct regions—the anterior segment and the posterior segment. The anterior segment includes the lens and extends from the outermost layer of the cornea to the posterior of the lens capsule. The posterior segment of the eye includes the anterior hyaloid membrane and all of the ocular structures behind it, such as the vitreous humor, retina, choroid, and the optic nerve.
Vitreoretinal procedures are commonly performed within the posterior segment of the human eye to treat serious conditions such as age-related macular degeneration (AMD), macular holes, premacular fibrosis, retinal detachment, epiretinal membrane, cytomegalovirus (CMV) retinitis, diabetic retinopathy, vitreous hemorrhages, and other ophthalmic conditions. Such procedures frequently require the severance and removal of portions of the vitreous humor (i.e., the “vitreous”) from the posterior segment of the eye, which is a colorless and gel-like substance that makes up approximately two-thirds of the eye's volume. The procedure for severing and removing the vitreous from the eye is referred to as a “vitrectomy.”
In a vitrectomy procedure, a surgeon inserts microsurgical instruments through one or more incisions made in the eye to cut and remove the vitreous from within. A separate incision may be provided for each microsurgical instrument when using multiple instruments simultaneously. The microsurgical instruments typically utilized during a vitrectomy procedure include: a vitrectomy instrument (e.g., treatment instrument) for severing and removing the vitreous body; an illumination probe for providing illumination within the intraocular space; and an infusion cannula for infusing fluid into the intraocular space to maintain intraocular pressure (TOP). In certain cases, to reach the vitreous located at peripheral regions of the eye, surgeons may also utilize a scleral depressor to displace the retina inward, in addition to other microsurgical instruments. Thus, during any given vitrectomy procedure, or any vitreoretinal procedure for that matter, three or more microsurgical instruments may be simultaneously used, whereas the surgeon only has two hands to perform the procedure.
The present disclosure generally relates to methods and microsurgical instruments for ophthalmic surgical procedures, and more particularly, methods and microsurgical instruments for vitreoretinal procedures.
In certain embodiments, a surgical instrument for performing an ophthalmic surgical procedure is provided. The surgical instrument includes a handpiece and a probe disposed through an opening in a distal end of the handpiece and configured to be inserted into an intraocular space of an eye. The probe further includes an infusion portion having a first diameter, and a treatment portion distal to the infusion portion and having a second diameter smaller than the first diameter. The infusion portion includes a port for directing fluid into a surgical site within the intraocular space and a channel fluidly coupled to the port for delivering the fluid to the port. The treatment portion includes a device for treating a tissue at a surgical site.
In certain embodiments, a system for performing an ophthalmic surgical procedure is provided. The system includes an endoillumination instrument and a treatment instrument for treating a tissue in an intraocular space of an eye. The treatment instrument includes a handpiece and a probe disposed through an opening in a distal end of the handpiece. The probe is configured to be inserted into the intraocular space of the eye, and includes an infusion portion having a first diameter and a treatment portion distal to the infusion portion and having a second diameter smaller than the first diameter. The infusion portion includes a port for directing fluid into a surgical site within the intraocular space and a channel fluidly coupled to the port for delivering the fluid to the port. The treatment portion includes a device for treating a tissue at a surgical site. At least one of the endoillumination instrument and the treatment instrument are configured to be manipulated by a surgeon to control a position of an eye during the ophthalmic surgical procedure.
So that the manner in which the above recited features of the present disclosure can be understood in detail, a more particular description of the disclosure, briefly summarized above, may be had by reference to embodiments, some of which are illustrated in the appended drawings. It is to be noted, however, that the appended drawings illustrate only exemplary embodiments and are therefore not to be considered limiting of its scope, and may admit to other equally effective embodiments.
To facilitate understanding, identical reference numerals have been used, where possible, to designate identical elements that are common to the figures. It is contemplated that elements and features of one embodiment may be beneficially incorporated in other embodiments without further recitation.
The present disclosure generally relates to methods and microsurgical instruments for ophthalmic surgical procedures, and more particularly, methods and microsurgical instruments for vitreoretinal procedures. In certain embodiments described herein, a vitreoretinal procedure is performed utilizing two surgical instruments: 1) a treatment instrument configured to a) treat a target ophthalmic tissue (e.g., sever and remove the vitreous body), and b) infuse fluid into the intraocular space to maintain intraocular pressure (IOP); and 2) an illumination probe for providing illumination within the intraocular space. The combined treatment and infusion functionalities of the treatment instrument eliminate the need to utilize a separate infusion cannula, thus enabling the vitreoretinal procedure to be performed with only two instruments and reducing the number of incisions made in the eye. Additionally, the utilization of two instruments facilitates easier manipulation of the eye by a surgeon, as one of the two instruments can be used to “steer” the eye during the procedure. Thus, the methods and instruments described herein enable not only improved safety during vitreoretinal procedures, but also improved procedural efficiency and control as compared to utilizing three or more instruments, or a single instrument.
Treatment portion 304 comprises a device that performs the treatment function of treatment instrument 200. For example, in embodiments where treatment instrument 200 comprises a vitrectomy instrument (i.e., a vitrector), treatment portion 304 performs a vitrectomy function, e.g., detaching vitreous from the retina and aspirating the vitreous from the eye. In such embodiments, treatment portion 304, and thus, treatment instrument 200, may comprise a mechanical vitrectomy device (e.g., a cutter), further described with reference to
Infusion portion 306 is arranged as an outermost surface of probe 302 and is disposed adjacent to treatment portion 304 such that at least a portion of treatment portion 304 is surrounded by infusion portion 306. Similar to treatment portion 304, infusion portion 306 extends distally from the distal end of handpiece 330, and may be directly or indirectly attached thereto within interior lumen 332. Infusion portion acts to direct infusion fluid into the surgical region. As shown, infusion portion 306 comprises one or more infusion ports 312 that direct infusion fluid into the surgical region. Generally, infusion fluid may be directed distally and coaxially with probe 302 by infusion portion 306. In certain embodiments, infusion portion 306 forms channel 314 leading to and fluidly coupled with infusion ports 312. In certain embodiments, channel 314 is a single, annular channel formed between infusion portion 306 and treatment portion 304. In other embodiments, a plurality of channels 314 are formed in infusion portion 306 and spaced about treatment portion 304. For example, a specific embodiment includes two channels 314 spaced about 180 degrees apart. In another specific embodiment, three channels 314 are spaced about 120 degrees apart. In certain embodiments, channel(s) 314 are formed as grooves in the inner surface of infusion portion 306. Fluid provided from, e.g., a fluid source may be fed to treatment instrument 200 and then to channel(s) 314 and out of infusion ports 312.
In the hybrid gauge probe 302 shown, infusion portion 306 has a larger diameter than treatment portion 304. It therefore has a larger cross-sectional distance than treatment portion 304. While the diameter of infusion portion 306 may be any suitable size, in certain embodiments, the diameter is selected to be within a range of about 15-30 gauge, and may, in certain examples, be selected to be within a range of about 18-27 gauge. Similarly, in certain embodiments, the diameter of treatment portion 304 is selected to be within a range of about 15-30 gauge, and may, in certain examples, be selected to be within a range of about 18-27 gauge. In specific embodiments, the diameter of infusion portion 306 is about 23 gauge, and the diameter of treatment portion 304 is about 25 gauge. In other specific embodiments, the diameter of infusion portion 306 is about 25 gauge, and the diameter of treatment portion 304 is about 27 gauge. In still other specific embodiments, the diameter of infusion portion 306 is about 27 gauge, and the diameter of treatment portion 304 is about 29 gauge. While described in terms of diameter, some embodiments have non-circular (non-cylindrical) outer surfaces, and therefore the cross-sectional distance may be used in place of diameter. For example, some probes/instruments may have a cross-section comprising an oval, quadrilateral, polygonal, or other shape.
Generally, infusion portion 306, which has a larger diameter than treatment portion 304, may span a longer distance along length L or probe 302 as compared to treatment portion 304 to provide optimal stiffness for treatment instrument 200, thereby improving ease of use and safety. In certain embodiments, treatment portion 304 spans a distance of between about 55% and about 95% of length L, such as a distance of between about 60% and about 90% of length L, such as a distance of about 75% of length L.
Generally, handpiece 330 has an outer surface configured to be held by a user, such as a surgeon. For example, handpiece 330 may be ergonomically contoured to substantially fit the hand of the user. In certain embodiments, the outer surface may be textured or have one or more gripping features formed thereon, such as one or more grooves and/or ridges. Handpiece 330 may be made from any materials commonly used for such instruments and suitable for ophthalmic surgery. For example, handpiece 330 may be formed of a lightweight aluminum, a polymer, or other suitable material. In some embodiments, handpiece 330 may be sterilized and used in more than one surgical procedure, or may be a single-use device. Handpiece 330 further includes one or more ports 334 at a proximal end thereof for providing ingress/egress for supply lines (e.g., a fluid supply line, vacuum supply line, power supply line, etc.) from various sources to be routed into lumen 332 of handpiece 3300. For example, port 334 may provide a fluid connection between handpiece 330 and a fluid supply line further coupled to a fluid source for infusion. In another example, port 334 may provide an optical connection between handpiece 330 and an optical fiber cable that couples to one or more light sources for providing laser light and/or illumination light. In certain embodiments, such sources are disposed in, or in communication with, a surgical console. The surgical console may include multiple functions, subassemblies, equipment, and other capabilities for performing one or more surgical procedures, including vitreoretinal procedures.
As shown, treatment portion 304, which extends distally from handpiece 330, includes outer tube 444. Generally, outer tube 444 may be formed of conventional surgical-grade materials, such as aluminum, stainless steel (e.g., 316 or 316L stainless steel), or other alloys. In particular examples, outer tube 444 is formed of Phynox, Elgiloy, or other suitable cobalt-chromium-nickel alloys, or nitinol or other suitable nickel-titanium alloys. Outer tube 444 comprises a closed end face 442 at distal end 440, which, in certain embodiments, may be beveled (e.g., disposed at a non-normal angle relative to a major axis of mechanical vitrectomy probe 402). Note that in other embodiments, end face 442 may be disposed at an angle normal to the major axis of mechanical vitrectomy probe 402. Outer tube 444 further comprises outer port 446, which is configured to receive tissue, such as ophthalmic tissue, for severing and aspirating. Outer port 446 is in fluid communication with inner channel 448 of outer tube 444, which further comprises inner tube 450 disposed therein. Inner tube 450 includes inner bore 452, open end 454, and cutting surface 456. In certain embodiments, inner tube 450 may further comprise inner port 455. Generally, inner bore 452 is in fluid communication with an aspiration line that connects to a vacuum pressure for pulling tissue into outer port 446 when inner tube 450 is located away from outer port 446. Inner tube 450 moves within inner channel 448 of outer tube 444 to cut tissue that is pulled into outer port 446 by the aspiration system. The ophthalmic tissue received by outer port 446 may include vitreous or ocular membranes.
When used to cut tissue, inner tube 450 may be initially moved away from outer port 446 and the vacuum pressure pulls tissue into outer port 446 and inner channel 448. Inner tube 450 then moves toward outer port 446 and severs the tissue within inner channel 448. The severed tissue is pulled through inner bore 452 of inner tube 450 by the aspiration system. In certain embodiments, severed tissue is pulled through inner port 455 of inner tube 450. Inner tube 450 then moves away from outer port 446, and the cutting process is repeated. A cutting cycle may include moving inner tube 450 to open outer port 446 and then moving inner tube 450 to close outer port 446 to initiate the cut, and then returning inner tube 450 to its starting position for the next cutting cycle.
Mechanical vitrectomy probe 402 further comprises infusion portion 306, as described in
As shown, treatment portion 304, which extends distally from handpiece 330, includes tube 544. In certain embodiments, tube 544 may have one or more portions formed of a translucent or transparent material, such as a plastic and/or polymeric material, and one or more other portions formed of more conventional surgical-grade materials, such as aluminum, stainless steel (e.g., 316 or 316L stainless steel), or other alloys. In certain embodiments, one or more portions of tube 544 may be formed of Phynox, Eligiloy, or nitinol. In the example of
Tube 544 comprises a closed end face 542 at distal end 540 of laser vitrectomy probe 502, which, in certain embodiments, may be beveled (e.g., disposed at a non-normal angle relative to a major axis of laser vitrectomy probe 502). Note that in other embodiments, end face 542 may be disposed at an angle normal to a major axis of laser vitrectomy probe 502. In
Note that in non-aspirating examples, tube 544 may not comprise port 546, and optical fiber 550 may terminate adjacent to end face 542, which may beveled.
The laser light and/or illumination light propagated and emitted by optical fiber 550 may be produced by one or more light sources 504 optically coupled to optical fiber 550. Such light sources 504 may be disposed in, e.g., a surgical console, with which laser vitrectomy probe 502 is coupled to via an optical fiber cable. In certain embodiments, the laser light produced by light source(s) 504 and propagated by optical fiber 550 is an ultraviolet (“UV”) (<350 nanometers (nm)) laser light. In other embodiments, the laser light is an argon blue-green laser light (488 nm), a Nd-YAG laser light (532 nm) such as a frequency-doubled Nd-YAG laser light, a krypton red laser light (647 nm), a diode laser light (805-810 nm), or any other suitable type of laser light for ophthalmic surgery. In certain embodiments, light source(s) 504 may produce a laser light that has a pulse rate within a range of about 10 kilohertz (kHz) and about 500 kHz. This range can effectively provide disruption of ophthalmic tissues, such as the vitreous. “Disruption” refers to the breaking down of tissue by rapid ionization of molecules thereof. Other pulse rate ranges can also provide disruption and are thus contemplated as well. In some examples, light source(s) 504 may produce a picosecond or femtosecond laser light. In some embodiments, light source(s) 504 may produce a continuous coherent laser light. For example, light source(s) 504 may produce a continuous coherent laser light at low power.
In embodiments where light source(s) 504 produce illumination light, the illumination light may include UV light, violet light, blue light, white light, infrared (“IR”) light, or any other suitable type of illumination light. In certain embodiments, light source(s) 504 include an LED-based (light-emitting diode based) illumination light source, a xenon-based illumination light source, or a halogen-based illumination light source. In certain embodiments, propagation of illumination light 562 through optical fiber 550 and into an intraocular space may be modulated by utilizing different types of illumination light sources, utilizing different materials for optical fiber 550, modifying the physical arrangement of optical fiber 550 within the laser vitrectomy probe 502, and/or by utilizing different materials for the probe.
In certain embodiments, optical fiber 550 is communicatively coupled to a digital visualization system, such as the NGENUITY® 3D Visualization System produced by Alcon. Other digital visualization systems, including those produced by other manufacturers, are also contemplated for use with the embodiments described herein. Utilization of a digital visualization system may enable modification of the color and intensity of, e.g., illumination light 562 emitted from optical fiber 550 by adjustment of hue, saturation, gamma, tint, and/or other light parameters.
While “light” is discussed herein, the scope of the disclosure is not intended to be limited to visible light. Rather, other types of radiation, such as UV and IR radiation, may be transmitted from optical fiber 550, and the term “light” is intended to encompass all types of radiation for use with optical fiber 550. In some examples, non-visible light may be transmitted by optical fiber 550 and captured by non-visible light sensors for analysis with the digital visualization systems described above. Thus, a non-visible light source may be coupled to optical fiber 550 in addition to an illumination light source and/or a laser light source, and the non-visible light may be propagated simultaneously with or sequentially pulsed with laser light 560 and illumination light 562.
As described above, optical fiber 550 is configured to project laser light and, in certain examples, illumination light. Utilization of a laser vitrectomy probe configured to project both laser light (for tissue severance) and illumination light may be beneficial since the projected illumination light may provide enhanced visualization of the intraocular space during severance and removal of the ophthalmic tissues, particularly when utilized in combination with a light pipe, e.g., light pipe 204. In certain examples, a single optical fiber 550, e.g., as shown in
Laser vitrectomy probe 502 further comprises infusion portion 306, as described in
To achieve the propagation depicted in
Cladding 572 may also comprise a transparent material, such as fused silica or glass. In some embodiments, cladding 572 is doped in addition to or instead of doping core 570. For example, cladding 572, which may comprise fused silica, is doped with a dopant that reduces the refractive index of cladding 572 relative to that of core 570. Example dopants include fluorine (F), chlorine (Cl), boron (B), or the like. Cladding 572, when doped, has a lower refractive index than core 570, thus enabling light guiding properties within core 570. Although one cladding 572 is depicted in each of
In certain embodiments, as depicted in
Note that although depicted as having different dimensions in
In
Regardless of whether the optical fibers 550a, 550b are contained within another structure in channel 548, optical fibers 550a, 550b may be arranged to either directly or indirectly contact inner sidewall 552 or be suspended without any contact with inner sidewall 552.
In one exemplary embodiment depicted in
Although many of the embodiments described above are generally directed to instruments for vitrectomies, the concepts exemplified therewith may be applied to instruments for other types of ophthalmic procedures. For example, other types of vitreoretinal procedures may be performed utilizing a treatment instrument with combined treatment and infusion functionalities, in addition to a light pipe or other endoillumination device.
As shown, treatment portion 304, which extends distally from handpiece 330, includes tube 644. In certain embodiments, tube 644 is formed of conventional surgical-grade materials, such as stainless steel and/or aluminum. In certain embodiments, tube 644 may have one or more sections formed of a translucent or transparent material, such as a plastic and/or polymeric material. Window 646 is press fit into tube 644 at distal end 640 of laser probe 602, and, as shown in
Tube 644 further comprises inner channel 648, which is at least partially defined by inner sidewall 652 of tube 644 and comprises optical fiber 650 disposed therein. Optical fiber 650, which may be substantially similar to optical fiber 550 in structure and material, is designed to operate as an optical waveguide and propagate laser light through a terminal end thereof. The characteristics of the laser light propagated through optical fiber 650 may be, in certain embodiments, such that the laser light may cause disruption of ophthalmic tissues, and/or in certain embodiments, such that the laser light may cause photocoagulation. In further embodiments, optical fiber 650 is also configured to propagate and emit illumination light for illuminating a surgical site. In still further embodiments, tube 644 may comprise two or more optical fibers for projecting laser light and/or illumination light; for example, one or more optical fibers may be configured to project laser light, while one or more additional optical fibers may be configured to project illumination light. Various examples of using single or multiple fibers for projecting laser light and illumination light are described above with reference to
In certain embodiments, a terminal end of optical fiber 650 is disposed against or terminates adjacent to window 646 such that the laser light projecting from optical fiber 650 will be projected distally through window 646 with sufficient power to sever ophthalmic tissues (e.g., vitreous) disposed distal to window 646, or to photocoagulate tissues (e.g., retinal structures) disposed distal to window 646. In the example of
The laser light and/or illumination light propagated and emitted by optical fiber 650 may be produced by one or more light sources 604 optically coupled to optical fiber 650. Such light sources 604 may be disposed in, e.g., a surgical console, with which laser probe 602 is coupled to via an optical fiber cable. In certain embodiments, the laser light produced by light source(s) 604 and propagated by optical fiber 650 is an ultraviolet (“UV”) (<350 nm) laser light. In other embodiments, the laser light is an argon blue-green laser light (488 nm), a Nd-YAG green laser light (532 nm) such as a frequency-doubled Nd-YAG laser light, a krypton red laser light (647 nm), a diode laser light (805-810 nm), or any other suitable type of laser light for ophthalmic surgery. In certain embodiments, light source(s) 604 may produce a laser light that has a pulse rate within a range of about 10 kilohertz (kHz) and about 500 kHz. This range can effectively provide disruption of ophthalmic tissues, such as the vitreous. However, other pulse rate ranges can also provide disruption and are thus contemplated as well. In some examples, light source(s) 604 may produce a femtosecond laser light. In some embodiments, light source(s) 604 may produce a continuous coherent laser light. For example, light source(s) 604 may produce a continuous coherent laser light at low power.
In embodiments where optical fiber 650 propagates illumination light, light source(s) 604 optically coupled therewith may generate UV light, violet light, blue light, white light, infrared (“IR”) light, or any other suitable type of illumination light. In certain embodiments, light source(s) 604 include an LED-based illumination light source, a xenon-based illumination light source, or a halogen-based illumination light source. In certain embodiments, propagation of illumination light through optical fiber 650 and into an intraocular space may be modulated by utilizing different types of illumination light sources, utilizing different materials for optical fiber 650, modifying the physical arrangement of optical fiber 650 within the laser probe 602, and/or by utilizing different materials for the probe. In some examples, non-visible light may be transmitted by optical fiber 650 and captured by non-visible light sensors for analysis with the digital visualization systems described above. Thus, a non-visible light source may be coupled to optical fiber 650 in addition to an illumination light source and/or a laser light source, and the non-visible light may be propagated simultaneously with or sequentially pulsed with laser light and illumination light.
In certain embodiments, optical fiber 650 is communicatively coupled to a digital visualization system, such as the NGENUITY® 3D Visualization System produced by Alcon. Other digital visualization systems, including those produced by other manufacturers, are also contemplated for use with the embodiments described herein. Utilization of a digital visualization system may enable modification of the color and intensity of, e.g., illumination light emitted from optical fiber 650 by adjustment of hue, saturation, gamma, tint, and/or other light parameters.
Laser probe 602 further comprises infusion portion 306, as described in
In
In the exemplary embodiment depicted in
Mechanical probe 702 further comprises infusion portion 306, as described in
In summary, embodiments of the present disclosure include methods, systems, and devices for performing vitreoretinal surgery. In particular, the surgical instruments described above include instruments combining the functions of treatment and intraocular infusion, thus eliminating the need to utilize a separate infusion cannula during a given vitreoretinal procedure. As a result, the vitreoretinal procedure may be performed with only two instruments (e.g., a treatment instrument and a light pipe for illumination), thereby reducing the number of incisions made in the eye. Additionally, the utilization of only two instruments facilitates easier manipulation of the position of the eye during a procedure by a surgeon, as one of the two instruments can be used to “steer” and stabilize the eye during the procedure. Accordingly, the methods and instruments described herein enable not only improved safety during vitreoretinal procedures, but also improved procedural efficiency and control as compared to utilizing three or more instruments, or a single instrument.
Although vitreous surgery is discussed as an example of a surgical procedure that may benefit from the described embodiments, the advantages of the surgical devices and systems described herein may benefit other surgical procedures as well.
A surgical instrument for performing an ophthalmic surgical procedure, comprising: a handpiece; and a probe disposed through an opening in a distal end of the handpiece and configured to be inserted into an intraocular space of an eye, the probe comprising: an infusion portion having a first diameter, the infusion portion comprising: a port for directing fluid into a surgical site within the intraocular space; and a channel fluidly coupled to the port for delivering the fluid to the port; and a treatment portion distal to the infusion portion and having a second diameter smaller than the first diameter, the treatment portion comprising: a device for treating a tissue at a surgical site.
The surgical instrument of Embodiment 1, wherein the device is a mechanical tool for manipulating the tissue at the surgical site.
The surgical instrument of Embodiment 2, wherein the device comprises scissors.
The surgical instrument of Embodiment 2, wherein the device comprises forceps.
The surgical instrument of Embodiment 1, wherein a distal end of the treatment portion comprises a beveled end face.
A system for performing an ophthalmic surgical procedure, comprising: an endoillumination instrument; and a treatment instrument for treating a tissue in an intraocular space of an eye, comprising: a handpiece; and a probe disposed through an opening in a distal end of the handpiece and configured to be inserted into the intraocular space of the eye, the probe comprising: an infusion portion having a first diameter, the infusion portion comprising: a port for directing fluid into a surgical site within the intraocular space; and a channel fluidly coupled to the port for delivering the fluid to the port; and a treatment portion distal to the infusion portion and having a second diameter smaller than the first diameter, the treatment portion comprising: a device for treating a tissue at a surgical site, wherein at least one of the endoillumination instrument and the treatment instrument are configured to be manipulated by a surgeon to control a position of an eye during the ophthalmic surgical procedure.
The surgical instrument of Embodiment 6, wherein the infusion portion has a diameter of 23 gauge and the treatment portion has a diameter of 25 gauge.
The surgical instrument of Embodiment 6, wherein the infusion portion has a diameter of 25 gauge and the treatment portion has a diameter of 27 gauge.
The surgical instrument of Embodiment 6, wherein the infusion portion has a diameter of 27 gauge and the treatment portion has a diameter of 29 gauge
The surgical instrument of Embodiment 6, wherein the infusion portion comprises 50% to about 60% and about 90% of a length of the probe.
The surgical instrument of Embodiment 6, wherein the infusion portion comprises 50% to about 75% of the length of the probe.
The surgical instrument of Embodiment 6, wherein the device is a mechanical tool for manipulating the tissue at the surgical site.
The surgical instrument of Embodiment 12, wherein the device comprises scissors.
The surgical instrument of Embodiment 12, wherein the device comprises forceps.
The surgical instrument of Embodiment 6, wherein a distal end of the treatment portion comprises a beveled end face.
The above-disclosed subject matter is to be considered illustrative, and not restrictive, and the appended claims are intended to cover all such modifications, enhancements, and other embodiments which fall within the true spirit and scope of the present disclosure. Thus, to the maximum extent allowed by law, the scope of the present disclosure is to be determined by the broadest permissible interpretation of the following claims and their equivalents, and shall not be restricted or limited by the foregoing detailed description.
Number | Date | Country | |
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63363739 | Apr 2022 | US |