Chandelier lighting fixture and method of manufacturing chandelier lighting fixture
Patent Information
- Application Number
- RU2024116288
- Authority / Receiving Office
- RU · RU
- Patent Type
- Patents
- Current Assignee / Owner
- Priority Date
- 2021-11-17
- Filing Date
- 2022-10-18
- Publication Date
- 2026-10-02
- Estimated Expiration
- 2042-10-18
Smart Images
Figure 00000001_ABST
Abstract
Description
CLAIM TO PRIORITY
[0001] This application claims the benefit of priority to U.S. Provisional Patent Application Serial No. 63 / 264,183, entitled "METHODS AND APPARATUS FOR WIDE ANGLE CHANDELIER ILLUMINATOR," filed November 17, 2021, and assigned to Qing Xiang, Timothy C. Ryan, and Yu Yan, which is hereby incorporated by reference in its entirety as if fully set forth herein.BACKGROUND OF THE INVENTION
[0002] During ocular surgery (e.g., including vitrectomy), the eye may be illuminated. Visualization, either directly or through a microscope, can be enhanced by using a chandelier illuminator. During ocular surgery, each of the vitrectomy probe needle and chandelier main body can be inserted through a pre-positioned cannula on the ocular surface. Each cannula provides a structurally supportive passageway strategically positioned in a misaligned area at the anterior surface of the eye, such as the pars plana of the ciliary body. This allows the probe needle or chandelier to be precisely inserted into the eye to avoid damaging the patient's crystalline lens or cornea.
[0003] Of course, to ensure a successful vitrectomy or other similar procedure, some additional instrumentation may be required. This means that if the light is used manually in conjunction with a more interventional instrument, such as a vitrectomy probe, the probe will need to be removed and replaced with another instrument. Therefore, the surgeon can continue to use their hand to hold the light. Of course, another surgeon or assistant can hold the light in place so that both hands are free to manipulate more interventional instruments. However, in the confined space of an ocular surgery, this may be impractical. Again, the surgeon's lack of control over the light can make it difficult to precisely direct the light to the desired area of the eye.
[0004] As an alternative to maintaining manual control of the illumination device, a pre-positioned chandelier can be used. Specifically, a flexible chandelier can be immobilized near the eye using a cannula (or inserted directly) and bent into a stable position. This allows the illumination device to remain in one position throughout the entire eye surgery. This allows the surgeon to freely manipulate several other interventional instruments without the need to maintain control of the illumination device.
[0005] Visibility and illumination issues exist for a variety of reasons. However, one of the primary reasons is due to size and dimensional limitations. For example, thanks to advances in minimally invasive design, a traditional chandelier-type illumination device can generally be smaller than approximately 25 gauge. This is an incredibly small amount of design space to work with. As a result, the light distribution from the fiber optic end of the illumination device can display a highly focused spot, with illumination sufficiently focused within a narrow target area of the eye.
[0006] Another reason for imperfect light distribution is that the small diameter of the fiber optic end is geometrically determined by a cutting tool during manufacturing. This means that the fiber optic end of the lighting fixture is shaped using a cutting tool to seal the end and ensure a certain degree of narrowing. Ideally, narrowing the fiber optic end using a cutting tool will provide improved light distribution.
[0007] Unfortunately, cutting the fiber optic end will likely result in a molded surface that is susceptible to scratches and deterioration in light distribution. Thus, although tapered cutting provides some improvement in light distribution, the effect is minimal. Overall, due to light distribution limitations, the surgeon may need to manually manipulate the light source to ensure that the light is directed where needed throughout the eye surgery. SUMMARY OF THE INVENTION
[0008] The device is designed for fixation in support of ocular surgery. The device comprises an optical end with an improved light emission design. Specifically, the device comprises a base with a substantially constant diameter that supports a tapered tip extending from the base. The tip has a predetermined length with a tapered angle and a predetermined bevel. The tip surface is uniquely polished to be substantially scratch-free and have uniform light scattering characteristics. DESCRIPTION OF GRAPHIC MATERIALS
[0009] Fig. 1 is a side sectional view of an embodiment of the optical end of a chandelier instrument with a unique design and surface for supporting eye surgery.
[0010] Fig. 2 is a perspective view of a grinding system for providing a unique surface finish for the optical end of Fig. 1.
[0011] Fig. 3 shows a general view in partial section of the eye prepared for a surgical operation carried out with the assistance of the device and the optical end of Fig. 1.
[0012] Fig. 4 is a partial sectional view of the eye during surgery performed with the assistance of the instrument and optical end as shown in Fig. 3.
[0013] Fig. 5 shows a graph that highlights the target manufacturability window for various designs of the optical end of the device according to Fig. 1.
[0014] Fig. 6A and 6B are block diagrams that summarize embodiments of the manufacture and use of the optical end of a chandelier device to assist in eye surgery.DETAILED DESCRIPTION
[0015] The following description sets forth numerous details to provide an understanding of the present invention. However, those skilled in the art will appreciate that the described embodiments can be practiced without these specific details. Furthermore, numerous variations or modifications can be employed that remain within the scope of the specifically described embodiments.
[0016] The embodiments are described with reference to certain types of surgical procedures with a vitrectomy probe. In particular, a procedure for removing vitreous humor to eliminate vitreous hemorrhage is illustrated. However, the instruments and techniques detailed herein can be used in a variety of other ways. Specifically, embodiments of chandelier devices can be used to assist instruments such as a vitrectomy probe in eliminating retinal detachments, macular pucker, macular holes, vitreous floaters, diabetic retinopathy, or a variety of other pathological conditions of the eye. Regardless of the circumstances, if an illumination device having an optical end with a unique design and a grinding surface for improved illumination of the interior of the eye is used to assist in the surgical procedure, a significant advantage can be obtained.
[0017] Referring now to Fig. 1, a side cross-sectional view of an embodiment of an optical end 100 of a chandelier device having a unique design and surface 175 for supporting a surgical operation on the eye is illustrated. The optical end 100 can consist of a fiber optic thread with a base 125, which is manufactured with an end cone 150. Further referring to Fig. 3, the end cone 150 is narrowed as illustrated to ultimately distribute a wide angle of beam divergence and ensure the distribution of light (330). Ultimately, although the chandelier device 350, which includes the optical end 100, can be in a fixed location during the surgical operation, sufficient light can be distributed throughout the interior of the eye 350 without the need for any change in the position of the device 350.
[0018] In the illustrated embodiment, the base 125 may have a diameter of approximately 300 micrometers to 600 micrometers, with the end cone 150 tapering from this point. This may correspond to current 23-29 gauge instruments. In the illustrated embodiment, the taper of the end cone 150 may reach a length (L) of less than approximately a millimeter, possibly from approximately 700 to approximately 850 micrometers. As illustrated, a taper extends along this entire length, giving the end cone 150 a conical appearance and character. In the illustrated embodiment, this taper may be defined by an angle (α) that is greater than approximately 8.5°. More specifically, the angle (α) may be from approximately 9° to 13°. As described below, when combined with a ground end conical surface 175, this type of design provides a light distribution 330 with a wide beam divergence angle (Θ) of greater than 100° (see Fig. 3).In the context of this document, the term "divergence angle" refers to the angle measured against the generally accepted full-width maximum (FW5%M) standard. However, other illuminance metrics may also be applicable.
[0019] In the illustrated embodiment, the end cone 150 is provided with a blunt end 160. The shape of the blunt end 160 can only make it possible to avoid the end cone 150 having an impractically sharpened tip, which may be prone to breaking off or becoming covered with cracks in such a way that it may create optical or other problems when working with the optical end 100. However, as in the case of the conical surface 175, the surface of the blunt end 160 can be formed by grinding and / or polishing, as further described below. However, as in the case of the conical surface 175, traditional mechanical cutting can be avoided to reduce the possibility of scratches or other non-dispersive or uneven surface characteristics.
[0020] Referring now to Fig. 2, a general perspective view of the grinding system 100 for providing a unique surface treatment for the optical end 125 of Fig. 1 is shown. That is, further referring to Fig. 1, as indicated above, the formation of the surface 175 is at least partially achieved by a grinding technique instead of traditional cutting. Thus, the end cone 150 is left with a surface 175 with an improved light distribution character. In the illustrated embodiment, the system 200 comprises a grinding plate 240 for providing special circular grinding by a grinding pad 275 attached to it. In one embodiment, circular grinding occurs in a non-uniform manner, in which the center of the rotating plate 240 changes location as the pad 275 rotates.Furthermore, in the context of this document, the term "grinding" may refer to grinding with a coarser pad material, as described below, or to a finer polishing. Regardless of the circumstances, the surface 175 of the end cone 150, from the fiber optics of uniform diameter to the shape of the end cone 150, is achieved using a technique that is less abrasive than that achieved by traditional cutting.
[0021] Referring again to Fig. 2, the grinding plate 240 and the pad 275 are guided by a drive element located below on the grinding table 260, although other system configurations can be used. Other hardware of the system 200 includes an orienting device 225 or a working holder, which is made at such an angle that it brings the tubular extension 250 to the pad 275. Thus, the fiber optic end 125 can be brought to the pad 275 with the required orientation to form a narrowed end cone 150 with an angle (α) illustrated in Fig. 1. The pad 275 can contain a grinding film. In one embodiment, the film is a 12 micrometer aluminum film that may contain silicate or diamond particles for fine grinding or polishing the fiber optics to the shape and contour of the end cone 150.In other embodiments, the film may range from approximately 1 to approximately 40 micrometers. Thus, the process can be considered one that transitions from polishing to grinding, each of which may be referred to as grinding herein. Regardless of the circumstances, improved taper geometry and surface treatment can be achieved to increase the divergence angle and smooth light distribution, as further described below.
[0022] The process of forming the narrowing of the end cone 150 by grinding, as described, can include periodic rotation of the fiber optic with the help of the tubular extension 250 or inside it. The working holder / orienting device 225 can be used to direct and maintain the inclined rotation of the fiber optic until the shape of the end cone 150 is obtained. At the same time, the directed rotation of the platform 275 according to a predetermined protocol is also supported by the system 200. In one embodiment, the end cone 150 is formed with a pointed end, which is later polished or ground to a blunt end 160 in Fig. 1 by the same system 200 by changing the orientation of the orienting device 225 to a vertical or perpendicular orientation relative to the platform 275 to continue the process and to form a blunt end 160.
[0023] In the illustrated embodiment, it should be noted that there is a bushing 280 of the device extending from the extension 250. This bushing 280 can be a structural component present in the finished form of the lighting device 300, as illustrated in Fig. 3, and can also provide additional stability or reliability to the fiber optics located underneath during the described grinding process. In the illustrated embodiment, the device 300 of Fig. 3 can be a 27 gauge device, which is mainly determined by the dimensions of the bushing 280, which constitutes the largest part of the device 300 that is to pass through the pre-positioned cannula 325, as described below. However, other suitable dimensions can also be used.
[0024] Referring now to Fig. 3, a general view in partial section of an eye 350 is illustrated, which is prepared for a surgical operation performed with the assistance of the device 300 and the optical end 100 of Fig. 1. In this view, the fixed nature of the chandelier device 300 is evident. This means that instead of being held in the hand, the device 300 is positioned in a fixed position so that further advancement of the optical end 100 is not allowed, and the optical end 100 provides light 330 from an unchanged position in the inner portion 310 of the eye. Given the limited size of the inner portion 310 of the eye, typically less than approximately 1 inch in diameter, this provides an element of safety for the surgical procedure to be performed. For example, the device 300 and the optical end 100 are not allowed to inadvertently reach or touch the optic nerve 360 or the retina 460 at the back of the eye 350 (see Fig. 4).In some embodiments, light 330 has an improved distribution with a divergence angle (Θ) exceeding 100° (other angles, such as less than or greater than 100°, are also possible). This optimizes visualization for the surgeon during the procedure. Again, this means that visualization is essentially unimpeded, while simultaneously freeing the surgeon's hand for other surgical tasks.
[0025] Referring again to Fig. 3, the pre-positioned cannula 325 is positioned in the sclera 370 displacement position in order to avoid damaging the more delicate lens 380, cornea 390, or other delicate elements in the anterior portion of the eye 350. Thus, the device 300 can engage with the cannula 325 and pass through it to advance the sleeve 280 and the optical end 100 to the illustrated position. To stabilize, the handle 340 of the device can be bent into a certain position, and other measures can be taken to secure the device 300 in place, for example, using medical tape.
[0026] As indicated, the divergence angle (Θ) of the light 330 emitted from the optical end 100 may exceed 100°. Further referring to Fig. 1, for an optical thread of approximately 350 micrometers to 450 micrometers, measured at the base 125, this can be achieved by using a tapering angle (α) of approximately 9° to 13° obtained by grinding. For the optical end 100, this corresponds to a tapering length (L) of approximately 700 micrometers to approximately 850 micrometers.
[0027] A larger beam divergence angle (Θ) can result in a smooth beam distribution without any hot spots or sharp beam edges. Additionally, the entire interior of the 310 eye can be comparatively brighter without any increase in light output compared to a traditional device.
[0028] Referring now to Fig. 4, a general view in partial section of the eye 350 is illustrated during a surgical operation performed with the assistance of the device 300 and the optical end 100, as shown in Fig. 3. In this view, the vitrectomy needle 400 is used to solve a problem with the eye, such as eliminating a hemorrhage in a certain area of the eye. This begins with the needle 400 being inserted through another pre-positioned cannula 425. Suction can be applied, and the port 477 of the needle 400 can be used to drain blood from the site of hemorrhage and the vitreous body. It should be noted that the cannula 425 is again positioned offset near the sclera 370. Thus, the more delicate cornea 390 and the lens 380 are again bypassed. Likewise, the optic nerve 360 is also very delicate.Thus, visibility may be key to ensuring that the needle 400 does not inadvertently contact the nerve 360, retina 460, or other delicate elements at the back of the eye 350.
[0029] This desired visualization is more than sufficiently ensured by the device 300 and the optical end 100, as illustrated in this document and described in detail above. Specifically, light 330 is provided that is smoothly and uniformly distributed with a divergence angle (Θ) exceeding 100 (see Fig. 3). As a result, not only the quality of surgical intervention but also the safety of the illustrated procedure are improved. Thus, despite other problems, such as the high probability of the surgeon's viewing angle being off-center, good illumination and visualization can be ensured for the procedure.
[0030] Referring now to Fig. 5, a graph is shown in which the target manufacturability window 500 is highlighted for various designs of the optical end 100 of the device of Fig. 1. In a real situation, the divergence angle results marked on the y-axis of the graph may vary by a degree or two relative to the simulated result curves illustrated in the graph of Fig. 5. However, the graph and these curves can provide a useful guide in terms of striving for repeatability of expected results as an aid in manufacturing.
[0031] Referring again to Fig. 5, and also further referring to Fig. 1, a fiber optic thread from approximately 375 micrometers to approximately 425 micrometers, measured at the base 125, can be used. With such a thread, and with ensuring a minimum divergence angle (Θ) of 100°, the light emission properties of different lengths and constriction angles can be considered. For example, different constriction angles (α) in the range from 8° to 14° are considered at different constriction lengths (L).
[0032] Depending on whether the tapering length (L) is 0.70 mm, 0.75 mm, or 0.85 mm, it becomes obvious that the expected divergence angle (Θ) will exceed 100° as long as the tapering angle (α) is within the illustrated range of 8° to 14°. For more accurate results, the manufacturer can try to narrow the range of tapering angle (a) variations to a peak window of 500, in which large divergence angles (Θ) can be repeatedly observed. In the illustrated embodiment, for the estimated tapering lengths (L), it is obvious that the minimum divergence angle (Θ) of 103° is obtained as long as the tapering angle (α) is from approximately 10° to 12°. Of course, the results may vary, and this is only an example of how such a 500 window can be established as an aid in manufacturing.
[0033] Referring now to Figs. 6A and 6B, block diagrams are shown illustrating embodiments of the manufacture and use of an optical end of a chandelier device for facilitating an ocular surgery. Specifically, as noted in 6A, an end cone with a tapered angle can be formed on the optical end of the fiber optic thread using the grinding system described in detail above in this document (see 610). The design parameters of the optical end can be predetermined in light of the tested and expected results, also described above. Regardless of the circumstances, by performing the predetermined grinding techniques used, the optical end can be included in a chandelier device for an ocular surgery, as indicated in 630. Thus, as shown in Fig. 6B, the illumination device can be fixed for an ocular surgery (see 650).This means that a divergence angle greater than 100° can be achieved through the optical end in the inner portion of the eye during surgery (see 670). As a result, as noted in 690, the surgical procedure can be performed without the surgeon having to manually hold the illumination device. Furthermore, this can be accomplished without compromising illumination of the inner portion of the eye.
[0034] The embodiments described above in this document include tools and techniques that enable the use of an illuminating device with a uniquely designed optical end to provide light emission over a wide angle. Again, the surface of the optical end can be formed or improved by grinding instead of traditional cutting to further improve the uniformity of distribution throughout the interior of the eye during surgery. The previous description has been presented with reference to currently preferred embodiments. However, other embodiments and / or features of embodiments that are disclosed, but not described in detail above, herein may be used.Furthermore, those skilled in the art and technology to which these embodiments pertain will appreciate that other modifications and variations of the described structures and operating methods can be practiced without substantially departing from the spirit and scope of these embodiments. Furthermore, the foregoing description should not be construed as applying only to the specific structures described and illustrated in the accompanying drawings, but rather should be considered consistent with and supportive of the appended claims, which provide the fullest and most reasonable scope of protection.
Claims
1. A chandelier-type illumination device for attachment during an ocular surgery, the device comprising an optical end having a light distribution characteristic and comprising: a base with a constant diameter of from 300 micrometers to 600 micrometers; a tapered end cone extending from the base, the tapered end cone having a length of from 700 micrometers to 850 micrometers with a taper angle greater than 8.5°; and an outer grinding surface of the tapered end cone formed by circular grinding, the surface having a uniform light scattering character, wherein the tapered end cone further comprises a blunt distal end formed by at least one of grinding and polishing; and wherein the tapered end cone is designed to provide a beam divergence angle of more than 100° with a smooth beam distribution in the absence of a hot center or a beam shape with sharp edges.
2. The device according to claim 1, wherein the tapered end cone is free of scratches and is adapted to distribute the beam divergence angle over 100°.
3. The device of claim 1, wherein the base diameter is from 350 micrometers to 450 micrometers and the taper angle is from 9° to 13°.
4. The device of claim 1, wherein the blunt distal end comprises an outer grinding surface.
5. The device according to claim 1, which further comprises a sleeve surrounding the base.
6. The device according to item 5, wherein the sleeve has a caliber of 27.
7. A method for manufacturing a chandelier lighting fixture, comprising: feeding a fiber optic thread into a grinding system to form an end cone with a taper angle of more than 8.5° over a taper length of 700 micrometers to 850 micrometers; incorporation of an end cone into a chandelier illumination device to assist the surgical procedure by providing a beam divergence angle from the end cone greater than 100°, wherein the feeding comprises using a grinding pad for grinding the outer grinding surface defining the end cone, while providing light distribution for the surgical procedure; in this case, the feed comprises circular grinding, which occurs in a non-uniform manner, in which the center of the rotating plate shifts as the circular grinding pad rotates, in this case the end cone is formed with a pointed end, and The grinding further comprises grinding the pointed end to a blunt distal end at the end cone.
8. The method of claim 7, wherein the grinding comprises polishing to form an outer grinding surface.
9. The method according to claim 7, wherein the grinding pad is a film that contains one of aluminum, silicate and diamond particles having a size in the range from 1 micrometer to 40 micrometers.
10. The method of claim 7, further comprising providing a bushing around the base of the chandelier lighting fixture.
11. The method according to claim 10, wherein the sleeve has a caliber of 27.
12. The method of claim 7, wherein the feeding further comprises periodically rotating the fiber optic.
Citation Information
Patent Citations
Directional backlight
EA031850B1
Thermally robust illumination probe tip
US20080177257A1
Eye Surgical Lighting Unit
US20150018629A1
Methods and apparatus for omnidirectional tissue illumination
US20150032190A1