IOL lens cutter tool

Abstract

This invention is related to currently developed and well-established surgery of cataract with Intraocular (IOL) lens. The current embodiment of the invention relates to solution of surgical and post-surgical situation of IOL lens when to remove implanted lens when it was not set properly or some damages observed or any uncomfortable situation is observed with some pathological condition with patients. The current embodiment is related with a tool which can cut the IOL lens to handle a very delicate situation where constrain of space and sensitivity of tissue is related. The current embodiment of the invention is related to cutting of intraocular lens of hydrophobic as well hydrophilic.

Description

[0001] FORM 2 THE PATENTS ACT, 1970 (39 OF 1970) & The Patents Rules, 2003 COMPLETE SPECIFICATION (See section 10; rule 13) 1. TITLE OF THE INVENTION: IOL lens cutter tool 2. APPLICANT(S) (a) Name: Dr Neha Dhokia (b) Nationality: Indian company 22 Kailash Darshan Kennedy bridge (c) Address: Nana chawk Mumbai 400005 3. PREAMBLE TO THE DESCRIPTION The following specification particularly describes the invention and the manner in which it is to be performed. Title: IOL lens cutter tool FIELD OF THE INVENTION The present invention relates to an intraocular lens cutting tool device used in ophthalmic surgery. The invention particularly relates to an ophthalmic lens system such as surgical cutting instrument for cutting or removal of intra-ocular lens (IOL). The invention specifically relates to a ‘v’ shaped surgical device for cutting or removing an intra-ocular lens implant. Moreover, the invention relates to a cutter or scissors for cutting of the lens used in ophthalmic surgery with tapered sides. BACKGROUND OF THE INVENTION The human lens is responsible for focusing the images on the back of the eye that are in the gaze of the eye. The human eye is somewhat analogous to a simple film camera. There are some lenses that focus the light at the front of the camera as in the eye. This focusing the light on the film or in the case of the eye the retina, which is a neurosensory membrane, that converts the optical image into neurological electrical activity that is transmitted to the vision center of the brain. If one thinks of the eye as a video camera that has a chip that converts the image to electrical activity and send it to the monitor which in the eye's case is the occipital lobe of the brain. Cataract is considered as one of the main cause for blindness in the world. The clouding of the human lens causes cataracts. In reality the human lens yellows and becomes less clear with age, when it clouds it is called a cataract. The cataract is somewhat akin to water that appears clear until it goes over a waterfall and appears white to the observer. In fact the word cataract is derived from the same Greek root for the name of a waterfall or cataract. It is estimated that globally there are approximately 100 million eyes with cataract causing a visual acuity less than 6 / 60, and this number is likely to be 3–4 times more for cataract surgery causing an acuity of less than 6 / 18. In the United States, there are more than 1,000,000 cataract extractions a year in the United States and this makes cataract surgery procedure one of the most commonly performed surgery. The complication rate is believed to be about 2%, which would be 30,000 cases a year of an intraocular mishap. There is probably a 20% incidence in this group of complications that are repairable by removing and replacing the intra- ocular lens implant. This necessitates the removal of approximately 6,000 implants a year with no standardized systems or management organization to remove these lenses. Cataract surgery is one of the most common procedures in the world with 10 million completed every year. A common and desirable method of treating a cataract eye is to remove the clouded, natural lens and replace it with an artificial IOL in a surgical procedure known as cataract extraction. An Intraocular lens (IOL) is a lens implanted in the eye usually as part of a treatment for cataracts or for correcting other vision problems such as short sightedness and long sightedness, a form of refractive surgery. If the natural lens is left in the eye, the IOL is known as phakic, otherwise it is a pseudophakia lens (or false lens). Both kinds of IOLs are designed to provide the same light-focusing function as the natural crystalline lens. This can be an alternative to LASIK, but LASIK is not an alternative to an IOL for treatment of cataracts. While usually a safe and permanent procedure, the intraocular lens that was originally placed can require removal and replacement in 3% of these cases. Cataract extraction results from removing the cloudy lens from the eye. This also causes the eye to lose its ability to focus light on the retina unless it is replaced. In days gone by the elderly cataract patient was relegated to a handicapped life only being able to see with extremely thick aphakic (no lens) glasses. In the recent past, patients had to spend 2 weeks in the hospital with sand bags around their head and never returned to a fully active life again due to the distortion of these glasses and the magnification and distortion issues, even with contact lenses. Cataract removal with intraocular lens implantation is one of the most performed surgical procedures in the world. Surprisingly, despite this huge demographic frequency, little is known about the total number of implantations performed in different areas of the world. Nowadays, indications for cataract surgery have expanded as a result of the excellent outcomes and high predictability of the technique. Such success has further promoted the indication of refractive lensectomy (lens removal with IOL substitution aiming to correct a refractive error), especially in high refractive errors, presbyopia, and in older age groups. Moreover, longer lifespans have also contributed to the pseudophakia population growing very quickly. Intraocular lens ex-plantation is today infrequent but may be potentially associated with serious complications. Phacoemulsification is also a cataract method in which the internal lens of the eye which has developed a cataract is emulsified with the tip of an ultrasonic hand piece and aspirated from the eye. Aspirated fluids are replaced with irrigation of balanced salt to maintain the volume of the anterior chamber during the procedure. This procedure minimizes the incision size and reduces the recovery time and risk of surgery induced astigmatism. It is best suited to relatively soft cataracts, where the ultrasonic energy required is moderate, and insertion of foldable intraocular prosthetic lenses, which take advantage of the small incision possible. It is the most common procedure for cataract removal in the developed world, with an excellent prognosis in uncomplicated cases. The phacoemulsification system comprises three sub-systems: Ultrasound, aspiration, and irrigation. Ultrasound: The ultrasound component is used to break the lens down into particles small enough to be aspirated through the suction passages around the tip, which allows a very small incision for access. The incision is small enough that sutures are not needed for closure, and very little astigmatism is caused by healing of the wound in the cornea. The phacoemulsification hand piece has a tip which vibrates longitudinally at a frequency in the range of 27 to 60 kHz, with a stroke length of 60 to 150 micrometers. Power is adjustable by the operator as a percentage of full power, and indicates a variation in nominal stroke length. Actual stroke length may vary slightly depending on the density of the material it contacts, though some instruments use feedback to maintain nominal stroke by adjusting current, voltage or frequency. Nominal frequency is not adjustable. Both efficiency and heat generation are increased with higher frequency, and 40 kHz is considered a good compromise and is in common use. There are various prior arts which discloses the various cataract lens removal process during the surgery. EP 0316085 B1 discloses a surgical cutting instrument for use in cutting and evacuating material from parts and organs of animal and human bodies. It specifically relates to vitrectomy hand pieces for providing irrigating and aspirating and cutting functions for cutting and removing vitreous, blood clots, and other material from the eye during intraocular surgery, and to such hand pieces which more particularly incorporate reciprocating cutters. US 2004 / 0243142 A1 discloses an intraocular device designed to cut or section an intra-ocular lens in the eye in order to remove it through the original small implantation incision. The device represents a departure from all present technology, which makes use of either a scissor or a snare like mechanism. This application discloses an extraction device for extracting a deformable intraocular lens, the extraction device comprising a retracting band that is extended for receiving and retracted for engaging the deformable intraocular lens and for drawing the engaged deformable intraocular lens in an enclosed manner against a cutting blade, wherein the deformable intraocular lens is drawn into and cut by the cutting blade as the retracting band is retracted. US 2016 / 0263781 A1 discloses an apparatus and method for manufacturing intraocular lenses. In certain embodiments, two mold components (an outer mold component and an inner mold component) of different composition may be employed. The outer mold may be composed of a metal or other refractory material and may serve as the outer die into which a lens forming material can be introduced. The inner mold component may be composed of a softer or more compliant material and may be deployed within the outer mold component. US 4,629,462 A discloses an intraocular lens for use as an artificial lens implant in the human eye. It specifically discloses an intraocular lens suitable for use as an artificial lens implant in the human eye, comprising a lens body having first and second position fixation members extending from opposite sides of the periphery of said lens body, each of said position fixation members comprising a stem portion having first and second ends, a coil portion having first and second ends, and a peripheral portion extending to a position such that it may engage the tissue of the eye, each of said coil portions being located between said lens body and the peripheral portion of its position fixation member, said first end of each of said stem portions being joined to said lens body, said second end of each of said stem portions being joined to said first end of its associated coil portion, said first and second ends of each of said coil portions cross each other as seen in a plane generally perpendicular to the axis to said lens body, each of said second ends of each of said coil portions being coupled to the peripheral portion of its position fixation member by way of a transverse portion which is generally transverse to a second plane coinciding with and passing through the axis of said lens body and through said peripheral portions of said first and second position fixation members such that when pressure is applied to said peripheral portions of said position fixation members towards said lens body, pressure is applied to said coil portions by way of said transverse portions to provide for flexibility of said position fixation members. EP 1572440 B1 discloses an apparatus and method for cutting an IOL optic from an IOL blank whereby the resultant IOL optic has a square edge and the cutting is performed in a combined linear and rotational cutting movement. In another aspect, an IOL optic is provided which includes a square edge and helically shaped striations formed therein to help reduce glare. The above prior arts discloses various method for intraocular lens removal from the eye. Many surgical instruments have been designed in the recent past to aid ophthalmic surgeons in removing vitreous, blood clots, cataracts, lenses and other matter from the eye. These instruments typically have an elongated probe defining a cutter at the distal end thereof, which is inserted into the body, for example into the eye through an incision in the cornea or sclera. The probe thereof is typically formed by coaxial inner and outer tubes wherein a port is provided in the outer tube adjacent the end and the inner tube moves relative thereto, and the inner and outer tubes cut the material as it is drawn in through the port. The excised tissue is aspirated by suction from the interior of the body part, such as the eye, possibly together with fluid, through the central lumen of the hollow inner tube, and is collected in a collection vessel. There are normal side effects associated with all priorly available intraocular lens removal process during surgery such as discomfort in the eye, anesthesia residual effects like grogginess, dizziness, or nausea, blurred vision, itchiness in the eye, redness in the white of the eye, dryness, irritation, or a feeling of grittiness in the eye, swelling in or around the eye, floaters, light sensitivity, visual halo effect. Sometimes, it is in requirement to reoperate or remove or replace the IOL lens. Some of the reasons are as broken haptic while implantation, wrong dipoteric power of implanted IOL, and opacified IOL intra ocular lens. The cutters available in the market such as IOL cutter in a small size which strengthen boons to IOL ex-plantation procedure. The 19-gauge instrument can fit through 1.2-mm paracentesis incision, according to surgeon. The technique of IOL fragmentation includes dissection of IOL optic part with specially designed scissors. These micro scissors designed for insertion through a paracentesis incision while the surgeon holds the optic through the phacoemulsification incision in to two or three parts. There is a technique to remove IOL by molecular cartage, but this can be only be done after 3.5 mm cut. However, the major challenge associated with all these scissors / cutters are process of managing and operating IOL removal because the most of the removal is done by incision of 2.7-3.5 mm. The major problem in removal of IOL lens after cutting is the successful removal of cut from surgery area and replacement with a new IOL. Another major hurdle is the movement of the scissors in folding and unfolding mode. As the area of the surgery is very sensitive, it is very difficult for the movement of scissors to cut the IOL lens surrounding these areas. Hence, there always remain an unmet need for a device which can solve the above mentioned problems associated with intraocular lens cutting. Further, there is always requirement of a patient compliant as well as a pain free procedure for removal or cutting of intraocular lens from the surgery area due to sensitive part. Therefore, the inventor of the present invention has focused on providing a solution for an easy procedure for removal of lens in surgical and post-surgical situation from the patient’s eye by an ophthalmologist. The inventor has discovered a ‘v’ shaped ophthalmic lens system such as surgical cutting instrument for cutting or removal of intra-ocular lens (IOL). Moreover, the invention relates to an intraocular lens tool device with tapered sides of cylindrical body for cutting the lens. SUMMARY OF THE INVENTION The present invention relates to an ophthalmic lens system such as surgical cutting instrument for cutting or removal of intra-ocular lens (IOL) and operate cataract. In a first aspect, there is described an intra ocular lens cutting tool in a cataract procedure. The lens cutting tool comprising a hub, a cylindrical body and a tip. In another aspect, the inventor of the present invention has discovered an intraocular lens tool having a ‘v’ shaped tip for cutting of intra-ocular lens which is coupled to the cylindrical body part. In another aspect, the present invention comprising an intraocular lens cutting tool with a ‘v’ shaped tip comprising a plurality of symmetrical cutting edge. The intraocular lens cutting tool comprising a ‘v’ shaped tip with a symmetrical cutting edge, wherein the tool can cut incision wound without stretching. In another aspect, an intraocular lens cutting tool comprising a cylindrical body having a tubular portion and tapered portion. The tapered portion of the cylindrical body is flattened from all sides towards the tip. The tapered portion of the cylindrical body has length ranges between about 5 mm to 30 mm. Moreover, according another embodiment of the present invention, an intraocular lens cutting tool can cut lens easily into two to five parts depending upon the need during the surgery. According to another embodiment, an intraocular lens cutting tool comprising a ‘v’ shaped tip which can cut all types of lens such as hydrophilic, hydrophobic or any other form of the intraocular lens. BRIEF DESCRIPTION OF THE DRAWINGS Numerous other objects, features and advantages of the invention should now become apparent upon a reading of the following detailed description taken in conjunction with the accompanying drawings, in which: FIG. 1 is a front side view of the high efficiency intra ocular lens cutting tool showing the substantially ‘v’ shaped front view of the tip having a plurality of symmetrical cutting edge. FIG.2 is a perspective view of a preferred embodiment of the high efficiency intra ocular lens cutting tool showing the cylindrical body having a tubular portion and tapered portion wherein the tapered portion substantially connected to ‘v’ shaped tip. FIG.3 is a rear left side view of the intra ocular lens cutter tool device. FIG.4 is a sectional front view of a ‘v’ shaped tip from front side for high efficiency intra ocular lens device. FIG.5 is an enlarged view of a cutting edge of the ‘v’ shaped tip responsible for cutting of lens. FIG.6 is a three-dimensional front view of an intra ocular lens cutting tool device with ‘v’ shaped tip showing tapered sides of the body. FIG.7 is a three-dimensional rear view of an intra ocular lens cutting tool device with ‘v’ shaped tip having a contacting and connecting end as well as showing narrow side and widened side of the tapered portion of the body. FIG. 8 is an open position of supportive jaws for collecting the intra ocular lens during cutting process. Fig. 9 is a closed position of supportive jaws for collecting the intra ocular lens during cutting process. DETAILED DESCRIPTION OF THE INVENTION The detailed description and the examples provided herein are exemplary and any modification or variation within the scope of the invention will be apparent to a person skilled in the art. Further, unless otherwise defined, all the technical and scientific terms used herein shall bear the meaning as understood by a person who is ordinarily skilled in the art. The “intraocular lens cutting tool” shall refer to a device or an apparatus which is used for the purpose of cutting / deforming / removing intraocular lens from eye during ophthalmic surgery process. Intraocular lens cutting tool can be interchangeable with intraocular lens extraction device or intraocular lens removal device or intraocular lens cutter or intraocular lens removable tool or a like thereof. The term “cataract surgery” also called as “lens replacement surgery” described as the lens removal from the human eye and usually replacing with an artificial intraocular lens. The natural lens of human eye has developed a cataract, an opaque or cloudy area which leads to blurred or loss of vision in the patients. According to the present invention, an intraocular lens (IOL) is a tiny, artificial lens for the eye. It replaces the eye's natural lens that is removed during cataract surgery. The lens bends (refracts) light rays that enter the eye, helping patients to see. According to the present invention, “phacoemulsification” or “phaco” is a method of cataract surgery in which the eye's internal lens is emulsified using ultrasonic energy and replaced with an intraocular lens implant or IOL. A “tip” refers to a portion that is proximate to the end side of the body of intraocular lens cutting device and that contacts the tissue to be deformed. A “body” refers to a portion of the intraocular device extending from the tip to the device mount and attached to the lateral part of the device. The “hub” portion refer to the lateral part of the device which is connected to the body part through screw or by any other suitable mechanism. The “cutting edge” refer to an inner side plain surface part of the tip portion which allows easy cutting and slicing of various tissues without incision. The “tubular portion” refer to a proximal portion of the cylindrical body which is in tubular form and attached by hub joint to the device. The “tapered portion” refer to a distal portion of the cylindrical body which is flattened from all sides towards cutting tip and allow easy handling of the device during surgery procedure without incision. Referring now to the drawings, wherein like numerals indicate like elements, there is shown in FIG. 1 an example of an intraocular lens cutting tool for extracting a deformable intraocular lens. The Fig 1 describes front side view of the Intra ocular lens cutting device having a ‘v’ shaped tip. The intraocular lens cutting device has a body part 1, a tip 2, a screw 3, and a hub 4. The tip 2 is in ‘v’ shape form or any other similar shape like thereof. The Fig.1 shows substantially ‘v’ shaped front view of the intraocular cutting tool. The present invention discloses a tip having a ‘v’ shaped cut or notch within the contacting end which provides optimum slicing or cutting action while also maintaining asymmetrical hand piece operation, an optimum ultrasonic cavitation field, and optimum aspiration. The present invention represents a ‘v’ shaped tip which can be utilized in the ultrasonic generator hand piece and provides the traditional ultrasonic and aspiration benefits and allows a surgeon to use the ultrasonic hand piece in any rotational axis position. The ‘v’ shaped nonmoving or fixed open tip 2 has a connecting end and a contacting end, yet the contacting end is uniquely shaped to provide the aforementioned cutting action. In a preferred embodiment, said connecting end contains a substantially ‘v’ shaped cut which provides the desired cutting or slicing action along with a desirable locus for uniform aspiration and ultrasonic field generation. The base of the ‘v’ shaped cut is placed opposite the contacting end, or towards to the connecting end. Accordingly, it is an object of the present invention to provide a high efficiency ultrasonic surgical aspiration tip having a ‘v’ shaped which promotes mechanical cutting and slicing of various tissues without incision. In one aspect of the invention, the body 1 has a cylindrical or tube like shape thereof. The cylindrical body ranges between about 5 mm to about 30 mm in length. Preferably, the cylindrical body in the present invention has length between about 15 mm to about 28 mm. The tip portion 2 is vibrated through body part 1 and it extends longitudinally out of the body 1 in order to engage an implanted deformable intraocular lens. The tip portion 2 has plurality of symmetrical cutting edges 5 showing open position of ‘v’ shaped tip 2. The tip 2 may have preferably two, three or more symmetrical edges 5 for cutting the intraocular lens. As the lens is drawn into the cutting tip, the lens is split into multiple parts and allowing it to be safely retracted from the posterior chamber. The ‘v’ shaped tip length size from about 5mm or less. Preferably, the length of the present invention tip has 2 mm or less. The ‘v’ shaped tip 2 is disposed at an angle between about 2 degrees to about 50 degrees as the maximum interior angle relative to a cylindrical body 1. Preferably, the tip is disposed at an angle of between about 15 to 45 degrees, and more preferably at angle of 35 degree to the cylindrical body 1. The ‘v’ shaped tip allows no stretching of the wound and skilled person can easily cut the intraocular lens into thinner sleeves. The ‘v’ shaped tip of the device is very safe for the endothelium part and posterior capsule. The screw 3 part contains zigzag shaped pattern for firmly holding screw during joint operation followed by straight pattern so that the hub 4 can joined in easy manner to body part 1 of the device. The screw 3 has length size between about 0.1 mm to about 5 mm in length, preferably 3 mm or less. The zigzag pattern of the screw has length size between about 3mm or less, preferably 2mm or less. The straight pattern has length size between about 2mm or less, preferably 1mm or less. A hub 4 is disposed at a proximal end of the device for engaging an ultrasonic hand piece (not shown) in order to couple ultrasonic energy to the needle body. The hub 4 is attached to the body part 1 by a screw 3 or any other possible joint mechanism. The hub 4 has length size ranges between about 2mm to 6mm, preferably between about 3mm to 5mm and more preferably about 2mm in the present invention. The entire intraocular lens cutting tool device has length in range from about between 10mm to about 40mm, preferably between about 25mm to about 30mm and more preferably about 28mm in the present invention. The Fig 2 describes a perspective view of a preferred embodiment of the high efficiency intra ocular lens cutting tool showing the cylindrical body having a tubular portion and tapered portion wherein the tapered portion substantially connected to ‘v’ shaped tip. A tubular portion 6 of the cylindrical body is attached one side to the hub joint and other side to the tapered portion 7. This tubular portion provides mechanical strength to the body part which helps firmly in holding entire device parts together during surgery procedure. The tubular portion 6 has length ranges between about 3mm to about 15mm, preferably between about 5mm to about 10mm and more preferably about 7mm in the present invention. The internal diameter of the tubular portion 6 has size between about 0.4mm to about 2mm, preferably between about 0.8 mm to about 1.5mm. The preferred internal diameter of the tubular portion 6 is 1.2mm in the present invention. The inventors of the present invention has discovered an intraocular lens cutting tool device with a cylindrical body 1 having a tapered portion 7. This tapered portion 7 has flattened surface from one or more side towards tip 2, preferably the flattened surface at two sides towards the tip. Because of this, a medical surgeon or ophthalmic practitioners can easily explant the intraocular lens without extending the wound in easy manner as well as no tilting of device occurs like what happens in other conventional cutting device. A tapered portion 7 of the cylindrical body is integrated to the one side at tubular portion 6 and to the other side at ‘v’ shaped tip 2. The tapered portion 7 has length ranges between about 3mm to about 25mm, preferably between about 10mm to about 20mm and more preferably about 15mm in the present invention. The cutting edges 8 of the ‘v’ shaped tip 2 in the present invention facilitates surgeon in making initial incision in the eye, and these cutting edges 8 works in conjunction with the ultrasonic power source to perforate the anterior capsule within the eye. Following this perforation, the cataract may be extracted. When used with the power source, the cutting edge 8 moves with a vibratory motion. The ‘v’ shaped tip 2 having a cutting edge 8 is disposed at an interior angle between about 5 degrees to about 90 degrees relative to a longitudinal axis of the cylindrical body 1. Preferably, the cutting edges 8 is disposed at an angle of between about 20 to 60 degrees, and more preferably at angle between about 30 to about 50 degrees to the cylindrical body 1. The blade 9 of the ‘v’ shaped tip 2 can cut intraocular lens at any angle between about 0 degrees to about 90 degrees, more preferably between about 20 to about degrees. The interior angle between the symmetrical cutting edges 5 of ‘v’ shaped tip 2 ranges between about 20 degrees to about 70 degrees, preferably from about 30 to about 50 degrees and more preferably about 35 degrees which can flexibly adjust all sides of the lens during ophthalmic surgery operation and cut the lens easily without undue efforts. The figure 3 describes a rear left side view of the intra ocular lens cutter tool device. The screw 3 part left side rear view is reflected in figure 3 in which zigzag pattern for the initial area of screw shown. The center part of the screw 10 joining the hub with the cylindrical body is shown in figure 3 and this center part 10 has round, circular or similar shape like that. The center part 10 has internal diameter ranges between 1mm to about 3 mm and preferably between about 2mm in the present invention. The figure 4 in the present invention describes a sectional front view of a ‘v’ shaped tip 2 from front side. The cutting-edge irregular shape pattern 11 shown in the middle of the figure 4 shows the sectional front portion of the ‘v’ shaped tip 2 in opposite direction as shown in dual mode. The figure 5 describes an enlarged view of a cutting edge of the ‘v’ shaped tip responsible for cutting of lens. The cutting edges 8 of the ‘v’ shaped tip 2 with a blade 9 is shown in enlarged view in the figure. The interior angle 12 between the cutting edges 8 and cylindrical body 1 describes the position of the tip 2 placement in the device. This interior angle can be adjustable as per the user’s requirement and depending upon the complexity of the surgery. The ‘v’ shaped tip 2 having a cutting-edges 8 disposed at an interior angle 12 between about 5 degrees to about 90 degrees relative to a longitudinal axis of the cylindrical body 1, preferably between about 35 to about 60 degrees and more preferably about 45 degrees which helps in easy slicing of tissue during surgery without any kind of incision. The figure 6 reflects a three-dimensional front view of an intra ocular lens cutting tool device with ‘v’ shaped tip showing tapered sides of the body. The tapered side 13 of the body part 1 is the inventor discovery of the present invention which is in flattened shape and due to this, the ophthalmic practitioners can easily explant the intraocular lens without extending the wound in easy manner. The figure 7 describes a three-dimensional rear view of an intra ocular lens cutting tool device with ‘v’ shaped tip having a contacting and connecting end. The contacting end 14 is a sharp top portion of the cutting edges 8 and this contacting end 14 contacts or touches first time to the tissue or endothelium of the human eye area during cataract surgery. The connecting end 15 is a bottom side portion (not reflected in figure) of the cutting edges 8 which attach directly to the tapered portion 7 of the body part 1. This connecting end 15 integrated firmly with the body part 1 and works in conjunction with the ultrasonic power source to perforate the anterior capsule within the eye. The figure 7 also describes about narrow side 16a and widened side 16b for tapered portion 7 of body 1 in intraocular lens cutting tool device. The figure 1 shows an internal diameter of the narrow side 16a of the tapered portion 7 between about 0.1 mm to about 1 mm, preferably between about 0.3 mm to about 0.7mm. The preferred internal diameter is 0.4 mm in the present invention. The figure 1 also shows an internal diameter of the widened side 16b of the tapered portion 7 between about 0.5 mm to about 3 mm, preferably between about 0.8 mm to about 2mm. The preferred internal diameter between about 1mm to about 1.1 mm in the present invention. The figure 8 describes an open position for supportive jaws 17 for collecting the intra ocular lens during cutting process. The space 18 shown between jaws describe about open position during cataract surgery process by which surgeon or ophthalmic practitioner can extract the cut portion of lens from surgery side without any hassle. The figure 9 describes a closed position 19 of supportive jaws 17 for collecting the intra ocular lens during cutting process. The closed space 19 reflected in figure 9 describes about the lens collected material inside the jaws and showing closed position. Intraocular lens cutting surgery is required when certain types of conventional ophthalmic surgery is unable to disrupt lens tissue and intraocular objects such as intraocular lenses or vitreous bodies so that they can be removed from the eye. The present invention utilizes a phacoemulsification process which uses ultrasonic energy of Phaco machine to emulsify the lens and aspiration to remove the lens emulsion from the eye, most preferably wound and endothelium portion during surgery. There are other methods of lens extraction which may include the use of instruments such as hooks, knives, or lasers to break the lens into pieces small enough to be removed through an incision in the cornea in an endoluminal approach. However, all these processes can be complicated and leads to incision and major cuts inside the eye during surgery. A typical phacoemulsification system includes a compact and console in operative communication with a phacoemulsification hand piece. Consoles typically include a cabinet that includes a power supply, a pump, electronics and associated hardware. The console provides control of the electronics of the hand piece, aspiration and irrigation. The hand piece includes a resonant rod attached directly to a set of piezoelectric crystals at a first end and a needle-like cutting tube on a second end. During phacoemulsification, the crystal provides the ultrasonic vibration required to drive the resonant rod and attached cutting tube. In a typical phacoemulsification procedure, a phacoemulsification tip extends through the distal end of an irrigation cannula and is inserted into the anterior segment of the eye through a small incision in the cornea. The phacoemulsification tip of the cutting tube is brought into contact with the lens of the eye such that the oscillating phacoemulsification tip emulsifies the lens. The emulsion is then aspirated through the lumen of the phacoemulsification tip along with any irrigation fluid supplied to the eye through the irrigation cannula during the procedure and directed to a waste container. The hub 4 as shown in figure 1 is joined by screwing 3 with phacoemulsifying probe. The probe is connected to the machine with its mechanism of the sonication the distal cutting tips with shape of ‘v’ mouth cuts the lens with minimum movement of the tip and with high shearing force the lens cut in to two or three parts and this can be supported by the serrated jaw 17 as shown in figure 8. In one embodiment, the ‘v’ shaped tip 2 having a plurality of symmetrical cutting edges 5 which cuts the lens with minimum movement inside the eye chamber and the tip can easily cut the wound by incision from 1 mm to 5 mm without stretching the wound. Preferably, the tip can cut the wound more than 2 mm without stretching during the surgery easily. In the present invention, each sleeve has 2 mm in width and can be removed gently and easily through a 2.2 mm incision without stretching or extending the wound at all. The tip is prepared by the medical grade stainless steels or any other suitable material. The phaco probe has to be primed just as usual with normal tip and then the tip is removed and the IOL cutting tip is screwed-in and tightened. The sleeve has to be attached. The forceps are such that the jaws of the forceps open and close vertically just like the mouth of a ‘v’ but the grip is such that it is horizontal and open and close parallel to the ground between the thumb and the middle of the index finger. It is ergonomically designed for ease of use. The tip is ergonomically designed for ease of use. The intraocular lens cutting tool device is manufactured from materials such as metal and their alloys or a like thereof. Preferably, the metals and alloys include but not limited to steel, stainless-steel, titanium or a like thereof. More preferably, the device is made from stainless steel of medical grade material. In another embodiment, the present invention intraocular lens cutting tool device can cut hydrophilic, hydrophobic or any other form of intraocular lens. The device can cut intraocular lens into 2 to 7 parts, preferably into 3 to 6 parts and more preferably into 4 to 5 parts easily without any hassle and without applying much exertion during surgery. Various modifications may be made to the presented embodiments by a person of ordinary skill in the art. Other embodiments of the present invention will be apparent to those skilled in the art from consideration of the present specification and practice of the present invention disclosed herein. It is intended that the present specification and examples be considered as exemplary only with a true scope and spirit of the invention being indicated by the following claims and equivalents thereof. While the foregoing describes an example or examples of the present invention, it is to be understood that such description is made by way of example only and is not intended to limit the scope of the present invention. It is expected that alterations and further modifications, as well as other and further applications of the principles of the present invention will occur to others skilled in the art to which the invention relates and, while differing from the foregoing, remain within the spirit and scope of the invention as herein described and claimed. Where means-plus-function clauses are used in the claims such language is intended to cover the structures described herein as performing the recited functions and not only structural equivalents but equivalent structures as well.

[0002] Claims: I / We claim that; 1. An intra ocular lens cutting tool for ophthalmic procedures comprising a hub, a cylindrical body and a tip. 2. The intraocular lens cutting tool according to claim 1, wherein the said tip is in ‘v’ shaped and having a plurality of symmetrical cutting edge and wherein the said ‘v’ shaped tip having a length about 5 mm or less. 3. The intraocular lens cutting tool according to claim 1, wherein the said cylindrical body contained solid tubular portion and tapered portion and cylindrical body has flattened surface from one or more sides towards tip. 4. The intraocular lens cutting tool according to claim 2, wherein the said ‘v’ shaped tip is disposed at an angle between about 2 degrees to about 50 degrees as the maximum interior angle relative to a cylindrical body and the interior angle between the symmetrical cutting edges of ‘v’ shaped tip ranges between about 20 degrees to about 70 degrees. 5. The intraocular lens cutting tool according to claim 7, wherein the internal diameter of the tapered portion ranges between about 0.1mm to about 3mm and cylindrical body has length ranges between about 1mm to about 30mm, wherein the said tapered portion of the cylindrical body has length ranges between about 3mm to 25mm and the said hub having a length between about 2mm to about 6mm. 6. The intraocular lens cutting tool according to claim 1, wherein the said tool can cut hydrophilic, hydrophobic or any other form of intraocular lens with range of into 1 to 5 parts, wherein the said tool can cut through than about 2 mm incision wound without stretching the wound.

Claims

I Claim; 1. An intra ocular lens cutting tool for ophthalmic procedures comprising a hub, a cylindrical body and a tip.

2. The intraocular lens cutting tool according to claim 1, wherein the said tip is in ‘v’ shaped.

3. The intraocular lens cutting tool according to claim 2, wherein the said ‘v’ shaped tip having a plurality of symmetrical cutting edge.

4. The intraocular lens cutting tool according to claim 1, wherein the said tool is manufactured from materials such as metal and their alloys or a like thereof.

5. The intraocular lens cutting tool according to claim 4, wherein the metals and alloys include but not limited to steel, stainless-steel, titanium or a like thereof.

6. The intraocular lens cutting tool according to claim 1, wherein the said cylindrical body contained solid tubular portion and tapered portion.

7. The intraocular lens cutting tool according to claim 1, wherein the said tapered portion of cylindrical body has flattened surface from one or more sides towards tip.

8. The intraocular lens cutting tool according to claim 1, wherein the said tool operates via phacoemulsification process using ultrasonic energy.

9. The intraocular lens cutting tool according to claim 1, wherein the said tool can cut through about 2 mm incision wound without stretching.

10. The intraocular lens cutting tool according to claim 2, wherein the said ‘v’ shaped tip having a length about 5 mm or less.

11. The intraocular lens cutting tool according to claim 2, wherein the said ‘v’ shaped tip is disposed at an angle between about 2 degrees to about 50 degrees as the maximum interior angle relative to a cylindrical body.

12. The intraocular lens cutting tool according to claim 3, wherein the said ‘v’ shaped tip having a cutting edge disposed at an interior angle between about 5 degrees to about 90 degrees relative to a longitudinal axis of the cylindrical body.

13. The intraocular lens cutting tool according to claim 3, wherein the said ‘v’ shaped tip can cut intraocular lens at any angle between about 0 degrees to about 90 degrees.

14. The intraocular lens cutting tool according to claim 3, wherein the interior angle between the symmetrical cutting edges of ‘v’ shaped tip ranges between about 20 degrees to about 70 degrees.

15. The intraocular lens cutting tool according to claim 7, wherein the internal diameter of the tapered portion ranges between about 0.1mm to about 3mm.

16. The intraocular lens cutting tool according to claim 1, wherein the said cylindrical body has length ranges between about 1mm to about 30mm.

17. The intraocular lens cutting tool according to claim 6, wherein the said tapered portion of the cylindrical body has length ranges between about 3mm to 25mm.

18. The intraocular lens cutting tool according to claim 1, wherein the said hub having a length between about 2mm to about 6mm.

19. The intraocular lens cutting tool according to claim 1, wherein the said tool can cut hydrophilic, hydrophobic or any other form of intraocular lens.

20. The intraocular lens cutting tool according to claim 1, wherein the tool can cut intraocular lens into 1 to 5 parts.

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