Cataract surgery instruments

Abstract

A cataract surgery instrument belonging to the technical field of medical surgical instruments, the cataract surgery instrument includes a direction guide tube (3), a deformation member (2), and a mesh bag (1), the end of the direction guide tube (3) has a notch (31) that communicates with its inner cavity (35), the deformation member (2) has a deformation portion (21) and a connecting portion (22) connected to the deformation portion (21), the connecting portion (22) is drilled into the inner cavity (35) and is movable along the axial direction of the direction guide tube (3), the mesh bag (1) is connected to the deformation portion (21), and the connecting portion (22) moves the deformation portion (21) and the mesh bag (1) along the axial direction of the direction guide tube (3), causing the deformation portion (21) and the mesh bag (1) to contract into the inner cavity (35) or expand out of the inner cavity (35). Cataract surgery instruments use a mechanical radial cutting method on the lens, which causes no thermal damage to intraocular tissues and is less likely to damage the posterior capsule, ligaments, and corneal endothelium. It shortens the operation time, is highly efficient, requires a small surgical incision, minimizes patient discomfort, allows for quick recovery, is easy to operate and learn, is inexpensive, and avoids the various adverse effects of ultrasonic vibration.

Description

[Technical Field]

[0001] The present invention relates to a cataract surgery instrument, which belongs to the technical field of medical surgical instruments. [Background technology]

[0002] Cataract is a common eye disease that causes blindness, in which the lens inside the eye becomes cloudy and opaque due to various causes such as aging, physical and chemical damage, and inflammation, blocking light from entering the eye and affecting vision. Common surgeries used to treat cataracts include traditional extracapsular cataract extraction, extracapsular extraction in which the lens is broken up and sucked out through a small incision, cataract phacoemulsification and artificial lens implantation, and femtosecond laser cataract surgery.

[0003] Traditional extracapsular cataract extraction has the following advantages over intracapsular extraction: it is performed under a surgical microscope, uses microsurgical instruments, and surgical techniques have all been greatly improved, creating the conditions for performing artificial lens implantation. However, it has the following disadvantages: it requires a large surgical incision, long surgery time, slow postoperative recovery, large incision, significant astigmatism, poor postoperative visual recovery, and requires the patient to be hospitalized.

[0004] Extracapsular cataract extraction, which involves crushing and extracting the crystalline lens through a small incision, lies somewhere between traditional large-incision cataract surgery and microinvasive phacoemulsification surgery. Compared to microinvasive phacoemulsification surgery, it requires larger incisions, more astigmatism, slower postoperative recovery, and longer surgical time. The incision typically reaches 5.5 mm, and the procedure takes approximately 15 to 30 minutes. It also carries a number of postoperative complications, including corneal hydrops due to corneal endothelial damage; iris damage resulting in hyphema and iris detachment; difficulty implanting an artificial lens due to posterior membrane rupture; and explosive choroidal hemorrhage. The most serious of these is intraocular infection. This procedure is suitable for use in areas that are economically underdeveloped or where phacoemulsification equipment is readily available.

[0005] The advantages of cataract phacoemulsification and artificial lens implantation are as follows: The surgical incision is small, compared to the conventional 12mm incision, which is 3mm, resulting in a milder surgical response, faster incision healing, and faster and better visual recovery. It also produces less postoperative astigmatism, making it easier to correct and control, safer, and more stable. The surgery takes less than 15 minutes. There is no need for hospitalization, allowing patients to return home after surgery, eliminating the need to wait for the cataract to mature before performing the surgery. It is painless for patients, and there are fewer surgical and postoperative complications. However, there are also unavoidable drawbacks, which are primarily determined by the physical properties of ultrasound. Specifically, these drawbacks are as follows:

[0006] 1. Unclear ultrasound range: During ultrasonic emulsification of cataracts, the range of ultrasonic action cannot be perceived by the surgeon. Moreover, the range of action is not limited to the vicinity of the opening of the ultrasonic emulsification needle, but also occurs along the energy transmission path. Therefore, the cataract disintegration and emulsification observed by people during surgery are merely results. The true microscopic process, the ultrasound itself, and its range and mode of action cannot be observed during surgery, which poses a great risk.

[0007] 2. Non-selective action of ultrasound: Not only does it act on cataracts, but the energy it transmits, the impact and cavitation it causes, can also induce physical and chemical changes in other tissues within the eye, easily damaging the eyeball.

[0008] 3. The invisibility of ultrasound effects: Most of the physicochemical changes in other tissues within the eye occur at the molecular level, making them microscopic processes that are impossible for people to detect. What people can see are the results. In fact, the results of these changes often occur with a delay, and the degree of these changes correlates with the magnitude of the ultrasound energy emitted during surgery.

[0009] 4. Cavitation effect of ultrasound: The repulsive force of ultrasound and the bubbles generated by cavitation affect the fluid dynamics during cataract evacuation.

[0010] 5. Mechanical effects of ultrasound (the propagation of ultrasound through a medium is a mechanical effect caused by reflection): It can induce several reactions in humans. Ultrasound's micro-massage of tissue intracellular substances causes the cell plasma to flow, causing cells to rotate and rub, thereby generating a cellular massage effect, also known as "internal massage." This is a unique characteristic of ultrasound therapy, which can change the permeability of cell membranes, stimulate the dispersion process of cell semipermeable membranes, promote metabolism, accelerate blood and lymph circulation, improve cellular ischemia and oxygen deficiency, improve tissue nutrition, change the rate of protein synthesis, and increase regeneration energy. It can also change the internal structure of cells, bring about changes in cellular function, and stretch and soften stiff connective tissue.

[0011] 6. The thermal effect of ultrasound is reflected at the boundaries of different tissues, forming standing waves, which cause intermolecular motion and friction, generating heat and easily damaging the eyeball.

[0012] Femtosecond laser cataract surgery uses computer-assisted precision to complete the most challenging step in traditional surgery, using focused femtosecond laser pulses to create incisions in the lens membrane, crystalline lens, and cornea. This allows the procedure to be perfectly tailored to the surgeon's specific needs, achieving new levels of surgical precision. Compared to traditional phacoemulsification surgery, femtosecond laser cataract surgery reduces the energy required for emulsification by 43% and the time required for emulsification by 51%. The incision is made with minimal force, avoiding potential damage to the eye from both human and instrumental sources. The entire process is fully computer-controlled and digitalized, completed with the femtosecond laser, ensuring precision and accuracy, reducing the standard deviation of surgeons' operations. The microscopic level is precise and predictable. Incision creation is accurate, reliable, predictable, and reproducible. However, the major drawbacks of this procedure are its high cost and lack of universal application.

[0013] The above surgeries have various drawbacks, so it is necessary to design a cataract surgery instrument that has various advantages such as a small surgical incision (less than 3 mm), a short surgical time, economical practicality, and universality, while also avoiding various damages such as the various adverse effects of ultrasonic vibration. Summary of the Invention [Problem to be solved by the invention]

[0014] To solve the above problems, the present invention provides a cataract surgery instrument that requires small surgical incisions during use, smaller than 3 mm, does not increase the number of existing incisions, does not require the use of ultrasound or laser, avoids the various adverse effects of ultrasonic vibration, and is less likely to damage the posterior capsule, ligaments, and corneal endothelium. It also has a short surgery time, high efficiency, minimal patient pain, and fast recovery. It is also simple to operate, convenient, practical, and inexpensive, and does not increase the patient's financial burden, making it economical, practical, and universally applicable. [Means for solving the problem]

[0015] The object of the present invention is to provide a cataract surgery instrument comprising: a directional guide tube having a notch at its end that communicates with the inner cavity; a deformation member including a deformation portion and a connection portion connected to the deformation portion, the connection portion being drilled in the lumen and movable along the axial direction of the direction guide tube; a mesh bag connected to the deformation portion, The purpose of the connection portion is to provide a cataract surgery instrument that moves the deformation portion and the mesh bag along the axial direction of the directional guide tube, contracting the deformation portion and the mesh bag into the inner cavity or expanding them outside the inner cavity.

[0016] In one embodiment of the present invention, the device further includes a push rod connected to the connecting portion for driving the connecting portion to move along the axial direction of the direction guide tube.

[0017] In one embodiment of the present invention, the device further includes an outer tube to which the direction guide tube is connected, and the push rod is drilled through the outer tube and the direction guide tube and connected to the connecting portion.

[0018] In one embodiment of the present invention, the direction guide tube includes a first tube portion and a second tube portion connected to the first tube portion, the notch is located at the end of the first tube portion away from the second tube portion, at least one boss is provided on the outer wall of the second tube portion, an opening groove that engages with the boss is opened at the end of the outer tube, and the direction guide tube is assembled to the opening groove.

[0019] In one embodiment of the present invention, a first chamber, a second chamber, and a third chamber are provided in the outer tube in this order, the cross section of the second chamber is smaller than the cross sections of the first chamber and the third chamber, and the direction guide tube is assembled to the first chamber.

[0020] In one embodiment of the present invention, the push rod includes a first rod body and a second rod body, the cross section of the first rod body is smaller than the cross section of the second rod body, the second rod body is drilled into the third chamber, and the first rod body is drilled into the first chamber and the second chamber and fixedly connected to the connecting portion.

[0021] In one embodiment of the present invention, a push portion is provided at the end of the second rod body away from the first rod body, and the push portion is located outside the outer tube and a plug is provided between the push portion and the outer tube.

[0022] In one embodiment of the invention, the size of the deformation is greater than the size of the lumen.

[0023] In one embodiment of the present invention, the deformation portion is a ring-shaped structure wound with a strip, the ring-shaped structure is an open ring structure or a closed ring structure, the material of the strip is a shape memory material, and the strip has a height of 0.01 to 2 mm and a thickness of 0.01 to 2 mm.

[0024] In one embodiment of the present invention, the mesh bag is a bag-like structure having an opening, knitted from a plurality of ultra-fine wires to form a plurality of meshes, and the opening of the mesh bag is connected to the strip. [Effects of the Invention]

[0025] Beneficial effects (1) The present invention adopts a radial cutting method for the lens. Mechanical radial cutting of the lens nucleus generates almost no heat and causes no thermal damage to intraocular tissues. Radial cutting of the lens nucleus is less likely to damage the posterior capsule, ligaments, and corneal endothelium. It is simple and easy to learn, has a short surgical time, is highly efficient, causes less pain to the patient, and allows for quick recovery. It is also simple to operate, convenient, and practical, is inexpensive, does not increase the patient's financial burden, requires small surgical incisions, does not increase the number of existing incisions, does not require the use of ultrasound or laser, and avoids the various adverse effects of ultrasonic vibration.

[0026] (2) In this invention, the expandable deformation part and mesh bag can easily enter and exit the interior of the eye through a small surgical incision. Once inside the eye, the deformation part expands the mesh bag to encase the cloudy lens nucleus. By pulling the connecting part, the deformation part contracts the mesh bag again, automatically tightening it and cutting the lens nucleus, completely fragmenting it. This mechanical radial cutting method for the lens allows the surgery to be completed with only a very small surgical incision, eliminating the need to increase the number of existing incisions. This significantly reduces damage to the patient's eye, shortens the patient's postoperative recovery time, and reduces surgical and postoperative complications, making it economical, practical, and universally applicable.

[0027] (3) The deformable portion of the present invention is a ring-shaped structure wound with a strip, and the ring-shaped structure is an open-ring structure or a closed-ring structure. The material of the strip is a shape-memory material with superelasticity, and the material deformation has memory properties and can quickly recover its memory properties after deformation, allowing it to smoothly enter and exit the eyeball through a small surgical incision.

[0028] (4) The mesh bag of the present invention is a bag-like structure with an opening, which is knitted from a plurality of ultrafine wires to form a plurality of meshes, and the opening of the mesh bag is connected to the strip. By controlling the number of ultrafine wires and the distance between the meshes, the size of the particles crushed from the lens nucleus can be controlled, and the strength of the ultrafine wires can cut the lens nucleus of any hardness. [Brief explanation of the drawings]

[0029] [Figure 1] 1 is a perspective view of a cataract surgery instrument of the present invention; FIG. [Figure 2] FIG. 1 is an exploded view of the cataract surgery instrument of the present invention. [Figure 3] 1 is a principal view of a cataract surgery instrument of the present invention; [Figure 4] 1 is a cross-sectional view of a cataract surgery instrument of the present invention. [Figure 5] 1 is an assembly diagram of the directional guide tube and outer tube of the present invention. [Figure 6] FIG. 2 is a cross-sectional view of the outer tube of the present invention. [Figure 7] FIG. 1 is a principal view of a push rod of the present invention. [Figure 8] FIG. 2 is a plan view of a deformable member of the present invention. [Figure 9] FIG. 2 is a perspective view of a direction guide tube of the present invention. [Figure 10] 1 is a cross-sectional view of a direction guide tube of the present invention. DETAILED DESCRIPTION OF THE INVENTION

[0030] Hereinafter, the technical solutions in the embodiments of the present invention will be clearly and completely described in conjunction with the drawings in the embodiments of the present invention. Obviously, the described embodiments are only some embodiments of the present invention, but not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative work fall within the protection scope of the present invention.

[0031] In the present invention, unless otherwise clearly specified and limited, the terms "coupled," "connected," and "fixed" should be understood in a broad sense, and may refer to, for example, a fixed connection, a detachable connection, an integral connection, a mechanical connection, an electrical connection, a direct connection, an indirect connection via an intermediate medium, an internal connection between two elements, or an interactive relationship between two elements. Those skilled in the art can specifically understand the specific meaning of the above terms in the present invention.

[0032] In the present invention, unless otherwise clearly specified or limited, a first feature being "above" or "below" a second feature may include direct contact between the first and second features, or may include additional feature contact between the first and second features that is not direct contact. Furthermore, a first feature being "above," "upper," and "on the upper surface" of a second feature may include the first feature being directly above and diagonally above the second feature, or may simply indicate that the horizontal height of the first feature is higher than that of the second feature. A first feature being "below," "below," and "on the lower surface" of a second feature may include the first feature being directly below and diagonally below the second feature, or may simply indicate that the horizontal height of the first feature is lower than that of the second feature.

[0033] Example 1 As shown in FIGS. 1 to 10 , this embodiment provides a cataract surgery instrument. The cataract surgery instrument includes a mesh bag 1, a deformable member 2, and a direction guide tube 3 having a notch 31 at its end that communicates with a lumen 35. The deformable member 2 includes a deformable portion 21 and a connecting portion 22 connected to the deformable portion 21, which is drilled into the lumen 35 and is movable along the axial direction of the direction guide tube 3. The mesh bag 1 is connected to the deformable portion 21, and the connecting portion 22 moves the deformable portion 21 and the mesh bag 1 along the axial direction of the direction guide tube 3, contracting the deformable portion 21 and the mesh bag 1 into the lumen 35 or expanding them out of the lumen 35. The expandable deformable portion 21 and the mesh bag 1 can easily enter and exit the eye through a small surgical incision. When the deformation part 21 enters the eye, it expands the mesh bag 1 to enclose the cloudy lens nucleus, and by pulling the connecting part 22, the deformation part 21 contracts the mesh bag 1 again and automatically tightens it, cutting the lens nucleus and completely fragmenting it. The present invention adopts this type of mechanical radial cutting method for the lens, which generates almost no heat and causes no thermal damage to intraocular tissues, allows the operation to be completed with only a very small surgical incision, does not require adding to the existing incisions, significantly reduces damage to the patient's eye, shortens the patient's postoperative recovery time, is less likely to damage the posterior capsule, ligaments, and corneal endothelium, reduces surgical and postoperative complications, is simple and easy to learn, has a short operation time, is highly efficient, causes less pain to the patient, and leads to a quick recovery. It is also easy to operate, convenient and practical, low-cost, economical, practical, and universal, does not increase the patient's financial burden, does not require the use of ultrasound or laser, and avoids the various adverse effects of ultrasonic vibration.

[0034] Optionally, it further comprises a push rod 6 connected to the connecting portion 22 for driving the connecting portion 22 to move along the axial direction of the direction guide tube 3 .

[0035] Optionally, the device further includes an outer tube 4 to which the direction guide tube 3 is connected, and the push rod 6 is drilled through the outer tube 4 and the direction guide tube 3 and connected to the connecting portion 22 .

[0036] Optionally, the direction guide tube 3 includes a first tube portion 32 and a second tube portion 33 connected to the first tube portion 32, the notch 31 is located at the end of the first tube portion 32 away from the second tube portion 33, at least one boss 34 is provided on the outer wall of the second tube portion 33, an open groove 44 is opened at the end of the outer tube 4 to engage with the boss 34, and the direction guide tube 3 is assembled to the open groove 44.

[0037] Optionally, a first chamber 41, a second chamber 42 and a third chamber 43 are provided in the outer tube 4 in this order, the cross section of the second chamber 42 being smaller than the cross sections of the first chamber 41 and the third chamber 43, and the direction guide tube 3 is assembled to the first chamber 41.

[0038] Optionally, the push rod 6 includes a first rod body 61 and a second rod body 62, the cross section of the first rod body 61 being smaller than the cross section of the second rod body 62, the second rod body 62 being inserted into the third chamber 43, the first rod body 61 being inserted into the first chamber 41 and the second chamber 42 and fixedly connected to the connecting part 22. Furthermore, the cross section of the second chamber 42 is larger than the cross section of the first rod body 61, so that the first rod body 61 passes through the second chamber 42 and is movable within the second chamber 42 along the axis of the direction guide tube 3.

[0039] As can be seen from this, the directional guide tube 3 is located in the first chamber 41, and the second rod body 62 is located in the third chamber 43. The second chamber 42, which has a smaller cross section, can play a restrictive role, so that the second rod body 62 of the push rod 6 can only move within the third chamber 43, and the deformation part 21 and the mesh bag 1 connected to the deformation part 21 can only move within the inner cavity 35 of the directional guide tube 3, thereby restricting the axial displacement of the deformation part 21 and the mesh bag 1 and preventing the deformation part 21 and the mesh bag 1 from being pulled out of the outer tube 4 by the push rod 6.

[0040] Optionally, a push part 63 is provided on the end of the second rod 62 away from the first rod 61, which allows the push rod 6 to be easily pushed and pulled, making it convenient to use. The push part 63 is located outside the outer tube 4, and a plug 5 is provided between the push part 63 and the outer tube 4. Optionally, a protrusion is provided on the end of the second rod 62 close to the first rod 61, with the cross section of the protrusion being larger than the cross section of the inner cavity of the plug 5. The plug 5 acts as a restriction, so that the second rod 62 of the push rod 6 can only move within the third chamber 43. The limit position for pulling out the push rod 6 is when the protrusion on the second rod 62 abuts against the plug 5, which effectively prevents the push rod 6 from escaping from the outer tube 4.

[0041] Optionally, the size of the deformable portion 21 is larger than the size of the lumen 35. The deformable portion 21 is in a deformed state within the lumen 35 and recovers its initial shape outside the lumen 35. The initial state of the deformable portion 21 may be, but is not limited to, an oval, a circle, a flattened shape, etc. Those skilled in the art can change the shape of the deformable portion 21 according to the use needs of the deformable portion 21. The deformed shape of the deformable portion 21 is a strip shape and is determined by the shape of the lumen 35.

[0042] Alternatively, the deformable portion 21 may have a ring-shaped structure wound with a strip, the ring structure being an open or closed ring structure, the strip being made of a shape-memory material, and the strip having a height of 0.01 to 2 mm and a thickness of 0.01 to 2 mm. Specifically, the ring wall depth of the deformable portion 21, i.e., the strip height, is 0.01 to 2 mm, and the ring wall thickness, i.e., the strip thickness, is 0.01 to 2 mm. The ring wall depth and ring wall thickness are set to allow free entry and exit without damaging the surgical incision as much as possible. The deformable portion 21 has superelasticity, and its material deformation has memory, allowing it to quickly recover its memorized shape after deformation, allowing it to smoothly enter and exit the eyeball through a 3 mm surgical incision.

[0043] Optionally, the mesh bag 1 is a bag-like structure with an opening, and is knitted from a plurality of ultrafine wires to form a plurality of meshes, and optionally, the diameter of the mesh is 0.01 to 4 mm, preferably 0.03 mm. The opening of the mesh bag 1 is connected to the strip. By controlling the number of ultrafine wires and the mesh distance, the size of the particles crushed from the lens nucleus can be controlled, and the strength of the ultrafine wires can cut the lens nucleus of any hardness.

[0044] Preferably, the characteristics of the lens nucleus are as follows: The lens nucleus becomes harder toward the central nucleus, exhibits a lenticular lens shape, has an anterior-posterior diameter of 4-5 mm, a diameter of 9 mm, an anterior radius of curvature of 10 mm, a posterior radius of curvature of 6 mm, a slightly flatter anterior surface than the posterior surface, and is approximately 3.6 mm from the anterior apex of the cornea. It is made of multiple layers of materials with different refractive indices, and becomes optically denser toward the center. There is a refractive index gradient from the anterior pole to the posterior pole and from the center to the equator. As a result, the lens hardness is insufficient due to the gradient from the periphery to the center, and becomes harder toward the central nucleus. Furthermore, since the cortex is present around the periphery of the lens nucleus, in addition to removing the length, the periphery and anterior and posterior surfaces of the lens nucleus are soft, further reducing the size. Therefore, it is necessary to encase the lens nucleus. The deformation portion 21 in this embodiment is preferably elliptical, with a vertical length of preferably 6.6 mm and a horizontal length of preferably 3.6 mm.

[0045] The operating principle of the present invention is as follows.

[0046] 1. First, pull the push rod to shrink the deformation part and the mesh bag into the lumen of the directional guide tube. Then, hold the surgical instrument in your hand and insert the notch at the front end of the directional guide tube into the eyeball through the 3mm surgical incision already made inside the eyeball. The notch at the end of the directional guide tube allows the directional guide tube to easily enter and exit the eyeball.

[0047] 2. Press the push rod to push the deformation member out of the lumen of the directional guide tube, and push the deformation part of the deformation member into the eyeball to restore and expand the memory shape, and then expand the deformation part and the mesh bag connected to the deformation part into the inside of the eyeball.

[0048] 3. Rotate the surgical instrument, restrict the lens nucleus with the auxiliary tool, and let the annular deformation encase the cloudy lens nucleus. At this time, pull the push rod to automatically tighten the deformation part and the mesh bag connected to the deformation part, cutting the lens nucleus. The ultra-fine wire on the mesh bag will crush the cloudy hard lens nucleus to the size of the mesh, completely crushing it. Then, the deformation part and the mesh bag will shrink into the lumen of the guiding tube, and the surgical instrument can be removed. The completely crushed cloudy lens can be washed away with the cleaning tool.

[0049] The present invention adopts a radial cutting method for the lens. Mechanical radial cutting of the lens nucleus generates almost no heat and causes no thermal damage to intraocular tissues. Radial cutting of the lens nucleus is less likely to damage the posterior capsule, ligaments, and corneal endothelium. It is simple and easy to learn, has a short surgical time, is highly efficient, causes less pain to the patient, and allows for quick recovery. It is also simple to operate, convenient, and practical, is inexpensive, and does not increase the financial burden on the patient. The surgical incision is small, so there is no need to increase the number of existing incisions. There is no need to use ultrasound or laser, and various adverse effects of ultrasonic vibration are avoided.

[0050] Although the present invention has been disclosed as a preferred embodiment as described above, it is not intended to limit the present invention, and any person skilled in the art can make various changes and modifications without departing from the spirit and scope of the present invention. Therefore, the scope of protection of the present invention should be determined based on what is defined in the claims. [Explanation of symbols]

[0051] 1. Mesh bag 2. Deformable member 21. Deformation part 22. Connection part 3. Directional guide tube 31. Notch 32, 1st pipe part 33, 2nd pipe part 34. Boss 35, lumen 4, outer tube 41, First Chamber 42, Second Chamber 43, Third Chamber 44, opening groove 5. Plug 6. Push rod 61. First rod 62, second rod 63, push part

Claims

1. A cataract surgery instrument comprising: a directional guide tube (3) having a notch (31) at the end thereof that communicates with the inner cavity (35); a deformation member (2) including a deformation portion (21) and a connection portion (22) connected to the deformation portion (21), the connection portion (22) being drilled into the lumen (35) and movable along the axial direction of the direction guide tube (3); a mesh bag (1) connected to the deformation portion (21), The connecting portion (22) moves the deformation portion (21) and the mesh bag (1) along the axial direction of the direction guide tube (3), causing the deformation portion (21) and the mesh bag (1) to contract into the lumen (35) or expand out of the lumen (35).

2. 2. The cataract surgery instrument according to claim 1, further comprising a push rod (6) connected to the connecting portion (22) for driving the connecting portion (22) to move along the axial direction of the direction guide tube (3).

3. The device further includes an outer pipe (4) to which the direction guide pipe (3) is connected, 3. The cataract surgery instrument according to claim 2, wherein the push rod (6) is drilled through the outer tube (4) and the direction guide tube (3) and is connected to the connecting portion (22).

4. The directional guide pipe (3) includes a first pipe section (32) and a second pipe section (33) connected to the first pipe section (32); 4. A cataract surgery instrument according to claim 3, characterized in that the notch (31) is located at an end of the first tube portion (32) away from the second tube portion (33), the outer wall of the second tube portion (33) is provided with at least one boss (34), the end of the outer tube (4) is provided with an opening groove (44) that engages with the boss (34), and the direction guide tube (3) is assembled into the opening groove (44).

5. 5. A cataract surgery instrument according to claim 4, characterized in that the outer tube (4) is provided with a first chamber (41), a second chamber (42) and a third chamber (43) in that order, the cross section of the second chamber (42) being smaller than the cross sections of the first chamber (41) and the third chamber (43), and the direction guide tube (3) being assembled to the first chamber (41).

6. The push rod (6) includes a first rod body (61) and a second rod body (62), 6. A cataract surgery instrument according to claim 5, characterized in that the cross section of the first rod body (61) is smaller than the cross section of the second rod body (62), the second rod body (62) is threaded into the third chamber (43), and the first rod body (61) is threaded into the first chamber (41) and the second chamber (42) and is fixedly connected to the connecting portion (22).

7. 7. A cataract surgery instrument according to claim 6, characterized in that a push portion (63) is provided at the end of the second rod body (62) away from the first rod body (61), the push portion (63) is located outside the outer tube (4), and a plug (5) is provided between the push portion (63) and the outer tube (4).

8. The cataract surgery instrument according to any one of claims 1 to 7, characterized in that the size of the deformation portion (21) is larger than the size of the inner cavity (35).

9. 8. The cataract surgery instrument according to claim 1, wherein the deformed portion (21) is a ring-shaped structure wound with a strip, the ring-shaped structure being an open ring structure or a closed ring structure, the material of the strip is a shape memory material, and the strip has a height of 0.01 to 2 mm and a thickness of 0.01 to 2 mm.

10. The cataract surgery instrument according to claim 9, characterized in that the mesh bag (1) is a bag-like structure having an opening, knitted from a plurality of ultra-fine wires to form a plurality of meshes with a diameter of 0.01 to 4 mm, and the opening of the mesh bag (1) is connected to the strip.

Images