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    • 专利摘要:
    Vitreoctomy device. A device (10, 30) for ocular surgery, comprising: a tube (1, 31), which in turn comprises a lower part (2) designed so that, during use of the device (10, 30), it remains in the inside of an eyeball, and an upper part (3) designed so that, during use of the device (10, 30), it is on the outside of the eyeball, said tube (1, 31) being configured to receive in its inside a surgical instrument or support for surgery or part of it; and at least one housing (4, 34) designed so that, during the use of the device (10, 30), it receives inside it at least one optical fiber (8) through which the eyeball is illuminated. The assembly formed by the tube (1, 31) and by the at least one housing (4, 34) is made of a single piece of transparent plastic material, designed to transmit the light emitted by said at least one optical fiber (8). ) towards the bottom of the tube (1, 31), illuminating the inside of the eyeball. (Machine-translation by Google Translate, not legally binding)
    公开号:ES2539523A1
    申请号:ES201331947
    申请日:2013-12-31
    公开日:2015-07-01
    发明作者:Antonio Palomino Muñoz；Roberto OÑATE GUTIÉRREZ；Eva RODRÍGUEZ VIDAL
    申请人:Fundacion Tekniker；
    IPC主号:
    专利说明:

    image 1
    DESCRIPTION VITREOCTOMY DEVICE 5 Field of the invention
    The present invention pertains to the field of medical devices and, in particular, to devices for eye surgery or vitreoctomy.
    10
    Background of the invention
    The operations in the so-called vitreous body of the eye (vitreoctomies) require an intraocular illumination with a probe, for example of optical fiber, being unnecessary to also carry a visualization beam (as it happens, for
    15 example, in an endoscope) since we have an exceptional window called a pupil to observe the inside of the eye.
    Traditionally, a small trocar has been used to leave one or more ports (usually three or more ports) implemented in the part of the eye known as "Pars Plana". It is thus possible to introduce through these ports, and selectively, either a light fiber, or serum infusion to maintain the shape and pressure
    20 of the eyeball, or the appropriate instruments for surgery (for example, a vitreotome).
    At present, these ports, mainly metallic, usually have a caliber that varies from 20 G to 27 G, the most common calibers being those of 23 G or 25 G. Their length is usually around 6 mm. They can be valved or not, to retain the ocular content.
    European patent application EP0501034A1 describes a probe for eye surgery through which
    25 introduce lighting devices. The perforations made in the eyeball are used for surgical intervention (usually one or two for the instruments and one for the infusion) to introduce a tube of about 1.5 mm in diameter that in turn carries about twenty internal wall optical fibers that form a lighting ring. This is an excessive and dangerous diameter. Note that 20G is the maximum gauge that is usually used (0.9 mm). In addition, the Pars Plana has a length of approximately 2 mm, so the
    30 diameter used in the device of EP0501034A1 is dangerous, since it implies a high risk of retinal detachments. The inside of each tube is free to introduce surgical instruments into the eye. It is thus achieved that the surgeon can have both hands free to operate, preventing one of them from devoting to the lighting system.
    However, the previous device requires a very specific configuration, in which the fibers are distributed
    35 through the inner wall of the tube. Also taking into account the small dimensions of the device, this makes its manufacture and handling very difficult. In addition, this device leaves the fibers open at the distal end of the probe, since they need to illuminate the ocular cavity. This carries the risk of fracture or detachment of any of these fibers inside the eye socket. This device also requires a base to be sutured to the ocular surface. Moreover, this device needs to occlude the
    40 device when there is no instrument inserted in the eye.
    Therefore, a lighting device for eye surgery is needed to solve the inconveniences of the state of the art, while allowing the surgeon to have both hands free to practice the intervention itself, avoiding dedicating one of his hands to hold the system of lighting. Description of the invention
    The present invention seeks to solve the aforementioned drawbacks by means of a device or trocar for eye surgery.
    In a first aspect of the invention, an eye surgery device is provided, comprising: a tube, which in turn comprises a lower part designed so that, during use of the device, it is inside an eyeball, and an upper part designed so that, during the use of the device, it is outside the eyeball. The tube is configured to receive inside a surgical or surgical support instrument or part thereof. The device also comprises at least one housing designed so that, during
    When using the device, receive at least one optical fiber inside through which the eyeball is illuminated. The assembly formed by the tube and the at least one housing is made of a single piece of a transparent plastic material at the visible spectral range, designed to transmit the light emitted by the at least one optical fiber towards the bottom of the tube, illuminating The inside of the eyeball. The light emitted by the at least one optical fiber is refracted with minimal losses towards the bottom of the tube. In this way, it is
    60 possible to illuminate the interior of the eyeball minimizing losses in light intensity.
    In one possible embodiment, the transparent plastic material is polymethylmethacrylate (PMMA). Alternatively, the transparent plastic material is polymethylpentane (PMP).
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    image3
    Preferably, the at least one housing is a tube.
    5 In one possible embodiment, at least a part of the outer perimeter of the lower part of the first tube is covered with an opaque material, so that the light coming from the at least one optical fiber only propagates through the uncovered area of the part bottom of the first tube. It is a material with a coating that provides a high reflection coefficient for the spectral range of the light source.
    10 Preferably, the distal end of the at least one housing is blind or closed, the end of the at least one optical fiber being unable to access the inside of the first tube.
    In a possible embodiment, the device further comprises a holding area or support zone, designed to, during the use of the device, support it outside the eyeball once the device has been introduced.
    15 lower part of the first tube inside said eyeball. In a more particular embodiment, that area of support or support area at least partially covers the upper part of the first tube and at least partially the at least one housing.
    In a possible embodiment, the end of the at least one optical fiber intended to be introduced by the at least one
    The housing is coated with means to prevent chipping of said at least one optical fiber and to maintain a tight fit of said at least one optical fiber. Preferably those means are a bushing.
    In one possible embodiment, the device comprises, in the at least one housing for receiving at least 25 an optical fiber through which the eyeball is illuminated, a lens to concentrate or focus the beam of light coming from the At least one optical fiber.
    In a possible embodiment, the device comprises two housings designed to receive at least one optical fiber inside the device through which the eyeball is illuminated.
    The invention also provides a system for eye surgery, comprising at least one device as described above, at least one optical fiber inserted into the at least one housing of the device and at least one light source designed to provide light to the at least one optical fiber of at least one device.
    Preferably the at least one optical fiber is coated, at its end inserted in the at least one housing, by means to prevent detachment of optical fiber pieces and to maintain a tight fit of the optical fiber.
    The advantages of the invention will be apparent in view of the description presented below. Brief description of the figures
    To complement the description and in order to help a better understanding of the characteristics of the
    The invention, in accordance with an example of practical embodiment thereof, is accompanied as an integral part of the description, a set of figures in which for illustrative and non-limiting purposes, the following has been represented:
    Figure 1 represents a scheme of the lighting and guidance device according to a possible
    50 embodiment of the invention. Figure 2 shows a longitudinal section of the lighting and guiding device schematized in Figure 1. Figure 3 represents a scheme of the lighting and guiding device according to an alternative embodiment of the invention. Figure 4 shows a profile view of an eyeball in which the device of the
    Invention. Figure 5 shows a perspective view of an eyeball in which three devices are implanted. Figures 6A and 6B refer to a first embodiment of the invention. Figure 6A shows a schematic representation of the guiding of the light from inside the body of the device or trocar 60 to the bottom of the retina. Figure 6B shows in detail the optical system inside the device or trocar 60. The
    Figure 7 shows the light intensity collected in the area of the retina in the example illustrated in Figures 6A and 6B. Figures 8A and 8B refer to a second embodiment of the invention. Figure 8A shows a schematic representation of the guidance of the light from inside the body of the device or trocar 60 to the vitreous body. Figure 8B shows in detail the optical system inside the device or trocar 80.
    65
    image4
    image5 Description of an embodiment of the invention
    In the context of the present invention, the terms "proximal" and "distal" refer respectively to the directions closest and furthest to the manipulator (eg, surgeon) of the device of the invention. In
    In other words, the distal part of the device is the one that is inserted or the one that is most deeply inserted in the patient's eye, while the proximal part of the device is the one that remains closest to the manipulator of the device. The distal part of the device remains at least partially out of the patient's eye.
    In the context of the present invention, the term "superior" is used to refer to a portion of the device that is proximal with respect to another portion of the device. And the term "lower" is used to refer to a portion of the device that is distal with respect to another portion of the device.
    Figure 1 shows a diagram of the guiding and lighting device for eye surgery according to a possible embodiment of the invention. The device 10 is formed by a hollow tube or main tube 1, 15 preferably of circular section. The hollow tube 1 is designed so that one part of the tube or lower part 2 is inside the eyeball during the surgical operation, and the other part of the tube or upper part 3 is outside the eyeball. In this way, the surgeon can introduce any apparatus, element, material or substance necessary for the intervention through the upper part 3 into the ocular cavity, passing through the lower part 2. Non-limiting examples of elements that can be introduced for tube 1 are scalpels, tweezers, vitrectors, infusions of serum, gas, silicone oil, additional light probes, etc. In addition, at the beginning of the surgery, a punch or trocar longer than the tube 1 itself is inserted along the tube 1 to puncture flat pars and thus leave the device of the invention inserted and self-adjusted in the eye. This is illustrated, for example, in Figure 5. The device 10 also comprises a housing, holding area or support area 5, which mainly serves to support the device in the eyeball once the lower part 2 of the tube 1 and also to grab it and facilitate its handling. This support area 5 is of greater section than the tube 1 to prevent the assembly from sliding into the eyeball.
    In a minimal configuration, not illustrated, this support or stop 5 is a widening of the outer surface of the distal area of the upper part 3 of the tube 1, for example as the part of Figure 1 referenced as 6 (but without the rest of the element identified as 5 in Figure 1). Preferably, this support or stop 5 has a cylindrical or substantially cylindrical shape, since it facilitates its manipulation and clamping with the thumb and index fingers. In a possible embodiment, the widening of the distal area of the upper part 3 occurs smoothly, establishing a smooth curve between the narrow part and the maximum perimeter of the support or stop 5. Unlike conventional devices, for example the one described in EP0501034A1 , this support or cap 5 no
    35 needs to be sutured or adjusted by for example an adhesive to the surface of the eyeball to immobilize the device 10 during surgery. On the contrary, the device remains self-adjusted in place without suturing the surface of the eye. That is, it is self-adjusting. This ensures that the lower part 2 does not penetrate more than is necessary.
    In an alternative configuration, the support or support 5 is a housing or knob that, in addition to the support 6 that forms the minimum configuration, has a cylindrical projection that further facilitates its manipulation. This configuration is shown in Figure 1 (reference 5).
    The device also comprises a second element, cavity or housing 4, also hollow. The extreme
    45 proximal of this housing 4 is open to the outside (through which the lighting for surgery is introduced, as explained below), while the other end (the distal end) is blind or closed. That is, it does not connect with the inside of the tube 1. One of the advantages of the distal end of the housing 4 being blind or closed is that it is ensured that there is no detachment of micro fibers into the main tube 1 , whereby the surgical instruments are introduced into the eyeball. In a preferred embodiment, the end of the housing 4 (distal end) is close to the height of the distal end of the upper part 3 of the tube 1. In other words, the end of the housing 4 is substantially at the height of the distal part of the tube. support or stop 5. That is, the blind end of the housing 4 is preferably located in the vicinity of the height of the tube 1 to which it, during surgical use, is introduced into the eyeball. In a possible embodiment, the element or housing 4 is an elongated tube, preferably of circular section.
    In a possible embodiment, not illustrated, at the proximal end of the tube 1 (that is, in the part that is outside the eye) a membrane is placed, preferably as a mitral valve, to act as a valve, so that ocular content is lost when there are no instruments inserted along the tube 1. Thanks to this membrane or valve, the device of the invention does not need plugs, unlike conventional devices. For example, the device described in EP0501034A1 needs plugs to occlude the device when it has no instruments inserted in the eye.
    Figure 2 shows a longitudinal section of the device 10, in which the main tube 1, the blind housing 4 and the support 5 are schematically observed. As can be seen, the distal end of the device 10, which coincides with the distal end of the main tube 1, is frustoconical, that is, it has a chamfer or angle, to image6 facilitate its insertion into the eyeball.
    image7
    tube length 1) preferably between 0.1 and 0.4 mm. More preferably, it measures between 0.2 and 0.3 mm. In a particular example, it measures 0.25 mm.
    As can be seen in figure 1, the support zone 5 can cover all or part of the upper part 3 of the first 5 tube 1. The support zone 5 can also cover the housing 4 totally or partially, provided it is free or open in it an entrance or access.
    This housing 4 is designed to introduce one or more light-carrying optical fibers 8 through the open end (proximal end). The optical fiber (s) 8 are connected to a light source (not illustrated in Figure 1).
    10 A plurality of optical fibers is preferably introduced 8. Note that it is preferable to use several high curvature fibers than a single fiber of less curvature. The light source can be any of the conventional ones for applications of this type. Preferably an LED light source is used. For example, and not limitatively, it is a Xenon light source.
    Figure 3 shows a diagram of a guiding and lighting device for eye surgery according to another possible embodiment of the invention. In it, it is provided that the device 30, in addition to the main tube 31, the support or housing 35 and the housing 34, comprises a second housing 39 that allows a second lighting input to be introduced (a second set of optical fibers, not illustrated ). This second housing 39 is similar to the first 34 (blind or closed) in size and shape, although it is also possible
    20 that presents some differences, depending on the areas of the eyeball that you wish to illuminate.
    Returning to Figure 1, in a preferred embodiment, during the surgical use of the device 10, the optical fiber (s) 8 are covered with a bushing 7 at its tip or end that is inserted through the housing 4 The bushing 7 is to ensure that there is no detachment of micro fibers towards the device 10 or towards
    25 the patient's eye, when introduced into the housing 4 of the device 10 and to maintain a tight fit so that the fiber does not come out in the time that the intervention lasts. In a preferred embodiment, the bushing 7 is made of stainless steel.
    To facilitate handling and use, the housing 4 (preferably a tube) is arranged forming a
    An angle between 15 and 45 degrees with respect to the top 3 of the first tube 1. In a preferred embodiment, this angle is between 25 and 35 degrees. In the embodiment of Figure 3, which has two housings 34 39, both are arranged forming said angles, one on each side of the main tube 31.
    The caliber of the device 10 (which is given by the caliber of the main tube 1) is preferably the caliber
    35 common in optical devices, that is, between 20 and 27 G. In a possible embodiment, the inner diameter of the main tube 1 is about 0.6 mm. The inner diameter of the tube should be so that a tool or equipment for surgery or surgery support can be introduced inside. As for the part of the device 10 30 that is inserted into the eyeball, that is, the lower part 2 of the tube 1 31, it has a maximum length of about 6 mm. In a preferred embodiment, the length of the lower part 2 of the tube 1 31 is about 4
    40 mm, so that the distance between the end of tube 1 31 and the bottom of the eyeball is about 20-24
    The assembly formed by the main tube 1 31, the housing 4 (or housings 34 39) and the housing, clamping zone or support zone 5 35, is formed by a single piece of a biocompatible transparent plastic material. That is, the piece has a main tube 1 31 that runs the piece from top to bottom and at least one cavity 4 34 39 open at one end and sealed at the inner end. In a preferred embodiment, this material is polymethylmethacrylate (PMMA), which stands out for its scratch resistance and for its transparency in the light emerging from the set of optical fibers. The piece is obtained by a process that can be molding, injection or extrusion, which is outside the scope of the present invention. Alternatively, the assembly can be implemented by any of the mentioned techniques, by other transparent plastic, as per
    50 example polymethylpentane (PMP) (also known as TPX® or TPX® RT18). The biocompatible transparent plastic material that the device 10 30 is made of has a mirror finish, that is, it does not absorb light. Material with specular finish is understood as the finish whose roughness varies between 5 and 20 nm.
    Because the tube assembly 1 31 and housing (s) 4 34 39 (and support 5 35) is made of plastic
    55 transparent, during surgery, the light that is introduced or along the housing 4 (and 34 39, if there were two housings) by means of the optical fiber (s) 8 is transmitted or diffused to the outside of the housing 4 34 39, illuminating the inside of the eye socket. In a preferred embodiment, a part of the outer perimeter of the lower part 2 of the tube 1 31 is covered with an opaque material to prevent light scattering. The largest possible coating of the outer perimeter of the bottom 2 of the tube is that covering
    60 from the proximal end of the lower part 2 of the tube 1 31 to the area of the opposite end where the tube 1 31 forms a chamfer or conical part (illustrated in Figure 2). In one possible embodiment, a piece of the lower perimeter of the tube 1 31 is left uncoated (ie, not just the chamfer part). Preferably, a part of the lower (distal) perimeter measuring (in the longitudinal direction of the tube 1) between 0.25 and 0.75 mm is left uncoated. It is chosen to leave this part uncoated so that the light is slightly dispersed and part of the interior is illuminated
    65 of the eyeball.
    image8
    image9
    It is thus achieved that the light emitted by the optical fiber (s) 8 only propagates through the lower part 2 of the tube 1 31 that is uncovered, including the open lower section, through which they are introduced into the eye socket surgical equipment and other accessories. In this way, a focused lighting can be achieved when the entire side wall of the lower part 2 of the tube 1 31 is coated, and a more scattered lighting when
    5 part of the light is also diffused through part of the side wall of the lower part 2 of the tube 1 31. Further, in relation to Figures 6A-6B and 8A-8B, two examples of devices according to the invention. The first one (figures 6A-6B) pursues the maximum use of the source's luminosity on the retina bottom, while the second one (figures 8A-8B) provides homogeneous and efficient illumination in the posterior chamber or vitreous body.
    10 Possible materials with which part of the outer perimeter of the lower part 2 of tube 1 31 is coated are any material that is biocompatible and opaque. That is, highly reflective to the emerging radiation of the set of optical fibers. In a preferred embodiment, this material is titanium. Alternatively, gold, platinum or others can be used. The material with which the tube is coated copies the specular finish thereof, to
    15 that the light does not go outside. This material is deposited on the outer perimeter of the tube 1 31 by conventional techniques that are outside the scope of the invention. For example, the cathodic evaporation technique is used.
    Also preferably, at the blind end of the housing 4 (or housings 34 39, if there is more than one)
    20 a lens is placed, not illustrated in Figures 1 to 3, but illustrated in the examples of Figures 6B and 8B, to concentrate or focus the light beams from the optical fiber (s) 8 and optimize its transmission along tube 1 31.
    The device solves problems derived from the prior art in a simple and efficient way. The device
    25 allows simultaneously and from a single port, to illuminate the inside of the eyeball and introduce the necessary surgical instruments or accessories inside.
    It is usual that, during the surgical intervention, two or three points of light are needed, to illuminate the intervention area. Figure 4 shows a view with a cut of the eyeball. It shows how a
    Device 30 of the invention has been introduced across the globe. In Figure 4, the device is supporting a surgical device, in this case a conventional punch (for example, a trocar with which the light port is inserted into the eye via pars plana). In figure 4 a second device 20 is shown nailed to the eyeball. This second device 20 can be either only a conventional trocar for the infusion of serum (1), additional to the point of light provided by the device 10 30 (also called trocar
    35) of the invention, or a second device such as that of the invention (ie, capable of simultaneously allowing to illuminate and introduce the infusion of the serum). That is, the additional trocars or ports can be like that of the invention or conventional, in which case they are formed by a tube through which one or more optical fibers are introduced. Preferably only the luminous ports or points of light of the invention are used, which can be up to two or three simultaneously. Note the great surgical progress of being able to perform
    40 only two wounds in Pars Plana: one with the ambient light port of the invention, where the infusion of serum necessary to maintain the pressure and shape of the eye during surgery is inserted, and another with the luminous port of the invention, which focuses on the retina, through which the necessary instruments are introduced. In either case, the optical fibers of each device can be connected to a light source of each device, or they can be connected to the same light source to which the optical fiber (s) is connected ( s) 8 of
    45 device of the invention. In a possible embodiment, the environmental trocar is also coated on the part that is introduced into the eyeball by an opaque material to prevent light scattering. For example, if the part of the environmental trocar introduced into the eyeball is 4mm, a part of it (from the part proximal or closer to the inner wall of the eyeball) is coated with said material. For example, the coated part measures longitudinally between 1 and 3 mm.
    In cases where it is required, for example, in the case of surgery that requires the use of both hands and two surgical equipment, two devices such as the invention are used. In this case, either the optical fiber (s) of each device is connected to a light source of each device, or the optical fiber (s) (s) of each device is (s) connected to a single light source, common to both (or more, if any)
    55 devices
    For example, in figure 5 an eyeball is shown in which three devices are implanted, where at least one is a device like that of figure 1 or figure 3, and the other two devices can be like the one of the invention or environmental trocars
    60 Therefore, an extremely efficient device is achieved, with better lighting and handling performance, which allows reducing the number of ports used per operation, thus reducing the risks and discomforts caused to the patient.
    65
    image10
    EXAMPLES
    Two examples of devices according to the present invention are described below, to facilitate illumination in transconjunctival vitreoctomy interventions. One of the devices pursues the maximum
    5 taking advantage of the luminosity of the source on the retina bottom, while the other provides a homogeneous and efficient illumination in the posterior chamber or vitreous body. Both devices allow the simultaneous use of tool and lighting source. Both the considered eye model and the light guidance have been modeled in the ZEMAX® ray tracing software.
    In both examples, a commercial LEDStar light source with a maximum light intensity of 15 lumens emitting in the visible range has been considered. For trocar / lamp modeling, trocars 23G and below (25G and 27G) have been used. The eye model considered is close to the Kooijman model, in which an emmetropic eye is considered where the surfaces are aspherical and the lens with a gradient in the refractive index is not considered.
    15 Example 1: Trocar for retina bottom illumination
    Figure 6A shows a schematic representation of the guidance of the emerging rays of the light source considered. Figure 6B shows in detail the design of the trocar (device 60) as well as the interior optical system by which the light is guided to the bottom of the retina.
    The device or trocar 60 has been designed in polymethylmethacrylate (PMMA) with a central hole of 752µm where the tool 65 of diameter 600µm is introduced. It has been considered an aluminum tool (Al) (high reflection coefficient). The outer part of the trocar or device 60 has a specular finish and it
    25 applies a highly reflective coating by means of which the light is confined in the coaxial cylinder formed between the tool 65 and the outer wall of the trocar or device 60.
    The optical system located inside the trocar or device 60 is constituted by an LED source guided by optical fiber with a diameter of 300 µm. Figure 6B shows the housing of the light source 63. The light beam is propagated through a machined hole in the trocar or device 60, at the end of which there is a commercial half-ball sapphire lens 64. Said lens 64 collects the light beam and focuses it on the coaxial cylinder located between the outer part of the tool 65 and the outer covering of the trocar or device 60. The choice of the lens has been carried out under the premise of compromise between two requirements : (1) focal point small enough to reach a minimum spot size at the coaxial cylinder inlet and therefore
    35 achieve maximum use of light intensity; (2) the lower limit of the focal length of the lens is marked by the minimum angle of exit of the rays from the bottom of the trocar 60. High values at the exit angles imply that part of the rays will not impact the bottom of retina and therefore the light intensity in said area will be reduced.
    After refracting on the half ball lens 64, the beam again undergoes refraction in the PMMA of which the trocar body or device 60 is constituted. By both refractions the beam is focused on the coaxial cylinder and undergoes multiple reflections between the tool 65 and the outer wall of the trocar or device 60. At the exit of the cylinder the light beam emerges with an opening such that it guarantees the illumination of the area that constitutes the retina bottom 68. It has been considered that the reflection in the external walls of the coaxial cylinder is from
    45 100%.
    Figure 7 shows the light intensity collected in the area of the retina (illuminance). 9 lumens of the 15 lumens emitted by the LED source reach the surface of the retina 68. Said percentage of losses is the sum of different contributions: losses in the entry of the light beam in the coaxial cylinder, losses in the multiple reflections inside the trocar or device 60 and the percentage of rays that do not impact the retina as a consequence of the high values in the angle of divergence. This last contribution is closely linked with the positioning of the trocar or device 60 in the eyeball. The light intensity distribution on the retina bottom 68 shows circular symmetry since it has been guided by a cylinder. In addition, an unlit central area can be observed, as a consequence of tool 65
    55 the central part of the trocar or device 60.
    Example 2: Lighting trocar for rear chamber / vitreous body
    Figures 8A and 8B refer to a second embodiment of the invention. Figure 8A shows a schematic representation of the light guidance from inside the body of the device or trocar 60 to the vitreous body 89. The tool 85 is also shown. Figure 8B shows in detail the optical system inside the device or trocar 80.
    In this case, lighting is required on the posterior chamber or vitreous body 89. Using it
    65 light source and a trocar design or device 80 based on the 23G, 25G and 27G, the optical system has been modified to achieve the required objective.
    image11
    image12
    To reach the illumination on the vitreous body it is necessary that the rays emerge from the final part of the trocar
    or device 80 with larger openings (see figure 8A). This is achieved by means of a half-ball lens 84 with a focal length shorter than that used in the previous case, as illustrated in Figure 8B. Figure 8B
    5 shows the detail of the optical system, which includes the light source housing 83. It can be seen that, maintaining the same design bases, a short focal length lens (f = 0.25mm) has been used by modifying the relative distances between source, lens and entrance to the coaxial cylinder.
    As in the case of retinal backlighting, the light source is housed in the duct 10 machined in the trocar or device 80, thus maintaining the relative source-lens distance and avoiding misalignment effects that may give place to loss of brightness in the area of interest.
    In this text, the word “understand” and its variants (such as “understanding”, etc.) should not be interpreted in an exclusive way, that is, they do not exclude the possibility that what is described includes other elements, steps, etc.
    In the context of the present invention, the term "approximately" and the terms of its family (such as "approximate", etc.) should be understood as indicative values very close to those accompanying the aforementioned term. That is, a deviation should be accepted within the acceptable limits from an exact value, since the person skilled in the art will understand that said deviation from the
    20 indicated values are inevitable due to inaccuracies in the measurement, etc. The same applies to the terms "around" and "substantially."
    On the other hand, the invention is not limited to the specific embodiments that have been described but also covers, for example, the variants that can be made by the average person skilled in the art (for example, in terms of the choice of materials, dimensions, components, configuration, etc.), within what follows from the claims.
    image13
    权利要求:
    Claims (12)
    [1]
    image 1
    1. A device (10, 30) for eye surgery, comprising:
    5 a tube (1, 31), which in turn comprises a lower part (2) designed so that, during the use of the device (10, 30), it is inside an eyeball, and an upper part (3 ) designed so that, during the use of the device (10, 30), it is outside the eyeball, said tube (1, 31) being configured to receive inside a surgical or surgical support instrument or part of the same; Y
    at least one housing (4, 34) designed so that, during the use of the device (10, 30), it receives at least one optical fiber (8) inside through which the eyeball is illuminated;
    the device (10) being characterized in that the assembly formed by the tube (1, 31) and by the at least one housing (4, 34) is made of a single piece of a transparent plastic material, designed to transmit the emitted light by said at least one optical fiber (8) towards the bottom of the tube (1, 31), illuminating the interior of the eyeball.
    fifteen
    [2]
    2. The device (10, 30) of claim 1, wherein said transparent plastic material is polymethylmethacrylate (PMMA).
    [3]
    3. The device (10, 30) of claim 1, wherein said transparent plastic material is polymethylpentane (PMP).
    [4]
    Four. The device (10, 30) of any of the preceding claims, wherein said at least one housing (4, 34) is a tube.
    The device (10, 30) of any of the preceding claims, wherein at least a part of the outer perimeter of the lower part (2) of the first tube (1, 31) is covered with an opaque material, so that the light from said at least one optical fiber (8) only propagates through the uncovered area of said lower part (2) of the first tube (1, 31).
    [6]
    6. The device (10, 30) of any of the preceding claims, wherein the distal end of said at least one housing (4, 34) is blind or closed, the end of said at least one optical fiber (8) being disabled to access the inside of the first tube (1, 31).
    [7]
    7. The device (10, 30) of any of the preceding claims, further comprising
    35 a holding area or support area (5, 35), designed to, during the use of the device (10, 30), support it outside the eyeball once the lower part (2) of the first has been introduced tube (1, 31) inside said eyeball.
    [8]
    8. The device (10, 30) of claim 7, wherein said clamping zone or support zone (5, 35) covers at least partially the upper part (3) of the first tube (1, 31) and at least partially the minus one accommodation (4, 34).
    [9]
    9. The device (10, 30) of any of the preceding claims, wherein the end of said at least one optical fiber (8) intended to be introduced by the at least one housing (4, 34) is coated
    45 of means (7) to prevent chipping of said at least one optical fiber (8) and to maintain a tight fit of said at least one optical fiber (8).
    [10]
    10. The device (10, 30) of claim 9, wherein said means (7) is a bushing.
    [11]
    11. The device (10, 30) of any of the preceding claims, comprising, in said at least one housing (4, 34) for receiving inside at least one optical fiber (8) through which it is illuminated the eyeball, a lens to concentrate or focus the light beams coming from the at least one optical fiber (8).
    The device (30) of any one of the preceding claims, comprising two housings (34, 39) designed so that, during the use of the device (30), to receive at least one optical fiber (8) inside it through which the eyeball is illuminated.
    [13]
    13. An eye surgery system, comprising at least one device (10, 30) according to any of the preceding claims, at least one optical fiber (8) inserted into the at least one housing (4, 34) of said at least one device (10, 30) and at least one light source designed to provide light to the at least one optical fiber (8) of said at least one device (10, 30).
    [14]
    14. The system of claim 13, wherein said at least one optical fiber (8) is coated, in
    65 its end introduced into the at least one housing (4, 34), by means (7) to prevent detachment of optical fiber pieces and to maintain a tight fit of said at least one optical fiber (8).
    image2
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    同族专利:
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    WO2015101624A1|2015-07-09|
    ES2539523B1|2016-01-13|
    引用文献:
    公开号 | 申请日 | 公开日 | 申请人 | 专利标题
    EP0201280A2|1985-05-01|1986-11-12|Kabushiki Kaisha TOPCON|Infusion instrument|
    US5632740A|1991-01-30|1997-05-27|Ceram Optec Industries, Inc.|Illuminated leading probe device|
    US5425730A|1994-02-16|1995-06-20|Luloh; K. P.|Illumination cannula system for vitreous surgery|
    ES2373368T3|2005-12-16|2012-02-02|Novartis Ag|ILLUMINATED INFUSION AND INCISION CANNULA.|
    US20110282160A1|2010-05-13|2011-11-17|Doheny Eye Institute|Self contained illuminated infusion cannula systems and methods and devices|
    ES1091361U|2013-07-17|2013-10-15|Antonio Palomino Muñoz|Luminous port for posterior vitreoctomy |
    US5478338A|1993-09-24|1995-12-26|Reynard; Michael|Fiber optic sleeve for surgical instruments|
    US5651783A|1995-12-20|1997-07-29|Reynard; Michael|Fiber optic sleeve for surgical instruments|
    WO2012021451A1|2010-08-09|2012-02-16|Alcon Research, Ltd.|Illuminated surgical instrument|US11173008B2|2015-11-01|2021-11-16|Alcon Inc.|Illuminated ophthalmic cannula|
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    ES201331947A|ES2539523B1|2013-12-31|2013-12-31|Vitreoctomy device|ES201331947A| ES2539523B1|2013-12-31|2013-12-31|Vitreoctomy device|
    PCT/EP2014/079447| WO2015101624A1|2013-12-31|2014-12-30|Device for vitrectomy|
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