US3884237A - Apparatus for intraocular surgery - Google Patents

Abstract

A pneumatically operated intraocular surgery apparatus which is of very light weight and small size, the part inserted into the eye having a diameter of 1 mm. or less. One embodiment of this invention employs a high frequency electric current electrode for cutting or severing vitreous or other material, said electrode being provided with means for removing coagulated material adhering thereto. Other embodiments of this invention which are also of very small size and light weight employ concentric tubes with a pneumatic means for moving one of the tubes with respect to the other at a slow or fast rate so that vitreous sucked into one of the tubes is sheared off by the sharp end of the other tube and the severed vitreous is sucked into a calibrated cylinder and at the same time saline solution is automatically supplied to the eyeball to replace the removed vitreous.

Description

United States Patent [191 OMalley et al.

[451 May 20, 1975 Primary ExaminerChannin g L. Pace Attorney, Agent, or Firm-Ben J. Chromy; Gerald L. Moore [57] ABSTRACT A pneumatically operated intraocular surgery apparatus which is of very light weight and small size, the part inserted into the eye having a diameter of 1 mm. or less. One embodiment of this invention employs a high frequency electric current electrode for cutting or severing vitreous or other material, said electrode being provided with means for removing coagulated material adhering thereto. Other embodiments of this invention which are also of very small size and light weight employ concentric tubes with a pneumatic means for moving one of the tubes with respect to the other at a slow or fast rate so that vitreous sucked into one of the tubes is sheared off by the sharp end of the other tube and the severed vitreous is sucked into a calibrated cylinder and at the same time saline'solution is automatically supplied. to the eyeball to replace the removed vitreous.

[ APPARATUS FOR INTRAOCULAR SURGERY [76] Inventors: Conor C. OZMalley, 1323 Gleneyrie Dr., San Jose, Calif. 95125; Ralph M. Heintz, Sr., 14734 Blossom Hill Rd., Los Gatos, Calif. 95030 [22] Filed: Dec. 5, 1973 [21] Appl. No: 422,097

Related U.S. Application Data [62] Division of Ser. No. 264,166, June 19, 1972, Pat. No.

[52] U.S. Cl. l28/303.14 [51] Int. Cl A61n 3/02 [58] Field of Search 128/303.14, 303.17

[56] References Cited UNITED STATES PATENTS 2,033,397 3/1936 Richman 128/303.17

2,102,270 12/1937 Hyams 128/303.17 2,828,748 4/1958 August.... 128/303.14 3,730,188 5/1973 Ellman l28/303.14

100 I03 I04 I02 #:213 121 Iuuumum SHEET 3 BF 5 SHEET 5 BF 5 PATENTEB HAY 2 01975 g .H mm 2 2.

APPARATUS FOR INTRAOCULAR SURGERY DESCRIPTION OF THE INVENTION This is a division of application Ser. No. 264,166 filed June 19, 1972 now US. Pat. No. 3,815,604.

This invention relates to apparatus for use in effecting intricate surgery such as performed by an ophthal mic surgeon.

In certain diseases of the eye or in certain trauma it is necessary to sever the vitreous which is a relatively complex substance composed of a framework of long protein molecules with patches of other protein molecules positioned at the intersections where the long protein molecules (collagen) are. In addition the vitreous also includes patches or balls of a second protein molecule (hyaluronic acid) which help to strengthen the vitreous and maintain its form and assist in holding water which comprises over 99 percent of the vitreous. The surgeon then finds it necessary to remove the severed vitreous or extraneous matter from within the vitreous and this removal must be accomplished without damage to the retina, to the choroid which underlies the retina or to the optic nerve or to the blood vessels associated therewith. This, of course, is no easy task as the vitreous cannot be cut by a scalpel or other similar instrument since the vitreous is relatively tough and simply folds over the edge of the knife and refuses to be severed. Various devices have been proposed for vitreous surgery and reference is made to such devices in the following published articles.

G. C. Couvillion, H. M. Freeman, and C. L. Schepens on pages 722 and 723 ofVolume 83, June 1970, Arch Ophthal, describe vitreous surgery using scissors. Robert Machemer, Jean-Marie Parel and E. W. D. Norton on pages 462 to 466 ofVolume 76, March-April 1972, Tr. Am. Acad. Ophth. and Otol., describe a vitreousinfusion-suction-cutter for vitrectomy. The cutter described in this article is provided with a rotating inner tube that is pushed by a spring against an end of an outer tube. A cutting hole which is slightly laterally displaced, is provided in the end of the tip. In another article entitled Experimental Vitrectomy, inVolume 86, November, 1971, Arch Ophthal, G. A. Peyman and M. A. Dodich describe an instrument for cutting vitreous strands by a chopping action produced by an inner tube against the plane end of an outer tube. The vitreous to be removed is drawn into the inner tube by suction provided in the inner tube. In this device another tube is attached alongside the outer tube and saline solution is supplied through this tube to replace the removed vitreous. In this device the chopping action is produced by oscillating the inner tube to 50 times per second and this is achieved by electrically energizing a small solenoid that is attached to the inner tube.

Probes energized by radio frequency electric currents have also been used in ophthalmic surgery and one such device is described by G. A. Peyman and N. A. Dodich onpages 29 to 37 of the January-February 1972 issue of Ophthalmic Surgery. This article describes the use ofa radio frequency electric current energized probe for intraocular coagulation. The May, 1954 issue of the American Journal of Ophthalmology contains an article by Angelos Dellaporta in which he describes a device using an insulatedtransbulbar needle 30 mm. in length which is connected to an electrical current supply and is used to seal retinal holes. This device, according to this article is manufactured by C.

Reiner, Mariannengasse, Vienna 9. The June, 1970 issue of Arch Ophthal contains an article by W. D. Cockerham, C. L. Schepens and H. MacKenzie Freeman entitled Silicone Injection in Retinal Detachment. The authors describe a procedure in which a 10 cc syringe which is attached to a blunted No. 18 or No. 20 needle is inserted into the eye through a meridional sclerotomy placed in the middle of the pars plana ciliaris for silicone injection.

It is therefore an object of our invention to provide an improved apparatus for cutting vitreous, severing adhesions and sealing blood vessels or severing them without causing hemorrhage.

Another object of our invention is to provide an improved device for operations such as cutting vitreous and sealing blood vessels that might be displaced or have become dislodged from the retina and migrated or grown into the body of the vitreous, said improved de vice enabling the surgeon to perform such operations with a minimum of likelihood of hemorrhage either while cutting the vitreous or during a separate procedure.

Still another object of our invention is to provide improved tools for use of eye surgeons, said tools being so small that they may be inserted into the eye through the pars plana.

A further object of our invention is to provide improved tools for use by eye surgeons, the portion of the tool to be inserted into the eye having a diameter of 1 mm., or less and the whole instrument being small and lightweight so that it can be hand-held and manipulated with ease and with minimal damage to the eye.

Other and further objects of our invention will be apparent to those skilled in the: art to which it relates or will be pointed out in detail in the following specification, claims and drawing.

By this invention we have provided the eye surgeon with an operating tool that is characterized by its extremely small size and light weight for performing surgery within the eye of the patient. We have developed two types of mechanical vitreous cutting instruments and one high frequency electrical cutting instrument. All of these instruments may of course be used for cutting material other than vitreous by the operating surgeon. One of the mechanical devices is referred to as the push-cut and the other is referred to as the pull-cut. Both of these instruments have the same dimensions and weight (about 4 grams) and in each case the length is about 2 inches overall with the body thereof having a length of 1 inch and the cutting tube also having a length of 1 inch. The diameter of the cutting tube is 0.035 inch (0.9 mm.). The push-cut instrument comprises a cylinder with a piston sliding within it and the cutting tube is rigidly fastened to the piston and passes through it to a debris extracting tube. This cutting tube is positioned inside of an outer tube and is free to slide about 0.020 to 0.040 inches (0.5l. mm.) between limits set by the cylinder head and piston. A narrow (0.05 mm.) slit is provided in the inner tube and this slit extends for a considerable length from the sharp cutting edge through one side of the tube. This slit permits the inner tube to be sprung out slightly so that the sharp ened end of the inner tube is pressed tightly against the inner surface of the outer tube thereby insuring a good shearing action when the sharp end of the inner tube passes the post opening in the outer tube. Vitreous to be severed is drawn into the port of the outer tube by suction and this vitreous is cut off when the piston moves the inner tube so that the sharp end thereof crosses the port of the outer tube. The frequency of the traverse of the cutting end of the inner tube across the port of the outer tube is controlled by an electrical circuit which generates timed electrical pulses for controlling air pressure and suction pulses to the piston of the cutting device. This frequency may be controlled by a foot actuated device which is operated by the surgeon employing this instrument. Thus, this frequency may be varied from a stationary condition with the port either open or closed to as many as 60 traverses per second or more. The speed of excursion is dictated by the nature of the material being cut, its proximity to the retina, the optic nerve, blood vessels or other sensitive regions. Air pressure and suction are applied to the piston of the cutting device through a flexible tube having a diameter of about one-eighth inch with a bore of about one-sixteenth inch. The debris tube is positioned inside of the pressure and suction tube and it has an outside diameter of about 0.035 inches and an inside diameter of 0.020 inches. Thus, the annular space between the two tubes serves to supply the cutting piston with suction and air pressure pulses and the inner tube supplies suction and conducts the debris out of the eye and into a measuring cylinder.

The pull-cut instrument has the same dimensions and weight as the push-cut instrument as previously mentioned but instead of cutting on the outward stroke of the inner tube this tube cuts on its inward stroke. Thus, the inner tube is, in this case, provided with the port and the material sucked into the port is sheared off by the sharpened end of the outer tube. In this case the outer tube is slit and is sprung inward so that it forms a tight fit against the outer surface of the inner tube. Also in this case the inner tube may be provided with two opposing ports thereby permitting easier flow of vitreous or other material into it. The pull-cut instrument has some advantage over the push-cut device, but it has the disadvantage that the inner tube must protrude about three-fourths mm. from the outer tube on each stroke. In all other respects the operations of both of the units are equally effective with the pull-cut instrument being less vulnerable to dulling of its cutting edge during assembly. However, with care either unit can be disassembled and reassembled without damage or difficulty.

The high frequency electrical cutting instrument that we have provided in this invention employs a radio frequency electrical supply and may be used equally well on frequencies between 13 megaHertz and 140 mega- I-Iertz. The source of high frequency power may be either of the thermionic variety or the solid state variety, however, the solid state is preferred because of its greater safety under all operating conditions. The radio frequency current is supplied to the cutting electrode through an impedance matching network and a coaxial transmission line terminated in the cutting device. The electrode is slidable in a dielectric sleeve which is of fused quartz provided with a thin outer coating of a fluorocarbon plastic. This coating provides a precautionary measure so that should the quartz tube break the pieces will be confined within the plastic sock and be withdrawn without damage to the eye. The fused quartz sleeve has a small hole of 0.005 inches diameter and the high frequency electrode which is attached to a small piston that is movable in the handle of the instrument is slidable in this quartz tube so that the cutting end of the electrode moves in and out of the end of the quartz a very short distance. During this in and out motion of the electrode tip any foreign matter such as coagulated protein adhering thereto is scraped off of the electrode by the end of the quartz tube. In order for this high frequency cutting instrument to function efficiently a reasonably good impedance match must be provided between it and the high frequency coaxial transmission line and in our invention we have provided such an impedance match in the handle of the device by adjusting the material of the dielectric sleeve and the diameter of the extendable flexible conductor.

In order to reduce the diameter of the high frequency cutting probe a metal tube may be employed instead of the fused quartz tube. Metals such as iridium or a platinum-iridium alloy may be used for this purpose because of its high strength, stiffness, hardness and chemical inertness. A metal tube having an outside diameter of 0.01 inches (0.25 mm.) is suitable for this purpose and this tube is provided with a coating of fluorocarbon plastic of 0.002 to 0.003 inches thickness. Such a tube is flexible enough so that it may not be necessary to provide a flexible hinge between it and the handle of the instrument as may be required in the case where a sleeve of fused quartz is used as previously described.

Further details and features of this invention will be set forth in the following specification, claims and drawings in which briefly:

FIG. 1 is a perspective view of an embodiment of this invention;

FIG. 2 is a schematic diagram showing the various controls provided to this apparatus;

FIG. 3 is a side view of the pneumatic control device provided to this invention;

FIG. 4 is a sectional view of the control device shown in FIG. 3;

FIG. 5 is an enlarged view of the pull-type vitreous cutting device;

FIG. 6 is an exploded view showing the parts of the vitreous cutting device shown in FIG. 5;

FIG. 7 is a sectional view taken along theline 77 of FIG. 6;

FIG. 8 is a sectional view taken along the line 8-8 of FIG. 6;

FIG. 9 is a sectional view taken along the line 9-9 of FIG. 6;

FIG. 10 is a greatly enlarged view of the cutting end of the pull-type device shown in FIGS. 5 and 6;

FIG. 11 is a greatly enlarged view of a modified form of the pull-type vitreous cutting device;

FIG. 12 is an enlarged view in perspective of the push-type vitreous cutting device;

FIG. 13 is an exploded view greatly enlarged of the cutting end of the device shown in FIG. 12;

FIG. 14 is a longitudinal sectional view of the device shown in FIG. 13 with the cutting elements assembled;

FIG. 15 is a fragmentary sectional view of the handle portion of the device shown in FIG. 12;

FIG. 16 is an enlarged view of the high frequency electric current energized cutting device employed in accordance with this invention;

FIG. 17 is a longitudinal sectional view of the device shown in FIG. 16; I

FIG. 18 is an exploded view of the device shown in FIGS. 16 and 17; and

FIG. 19 is a schematic view of a system for injecting normal saline solution or other liquid into the eye as material is removed from the eye.

Referring to the drawing in detail reference numeral designates a cabinet for housing various controls such as shown in FIG. 2 of the drawing and provided to this apparatus. The motor 11 which is mechanically connected to thevacuum pump 12 andair pressure pump 13 is housed in thecabinet 10 together with thepumps 12 and 13 which are connected by suitable tubes to thetanks 14 and 15, respectively. Avacuum gauge 16 is connected by suitable tube to thetank 14 and apressure gauge 17 is connected by a suitable tube to thepressure tank 15. These gauges are located on the front panel ofcabinet 10 so that the dials thereof are visible to the operator. The motor 11 is connected to a suitable source of electric power such as is available in the conventional wall outlet and aswitch 18 is provided on the panel of the cabinet for turning the motor on and off. Anauxiliary switch 19 is provided between the power line and the DC.power supply 20 which converts the alternating current supplied thereto to direct current for energizing themultivibrator 21 and flip-flops 22 and 23.

Multivibrator 21 is provided for triggering theflipflop 22 which produces an output designated as mode A signal which may be supplied to thegate 24 throughswitch 25 when it is desired to actuate thesolenoid 26 driving thevalve 27 in this mode. In mode A thevalve 27 is actuated to connect theoutput line 28 for equal intervals to thevacuum line 29 and thepressure line 30 alternately. When theswitch 25 is shifted to connect the output of flip-flop 22 to flip-flop 23 then the apparatus is operated in mode B and the wave form of this mode is supplied to thegate 24 and to solenoid 26 for controlling thevalve 27 in accordance with this mode. In mode B the valve 27is operated so that it connects theoutput line 28 to the vacuum orsuction line 29 for an interval approximately three times as long as the interval during which thisline 28 is connected to thepressure line 30. On the other hand the mode B signal may be used to connectoutput line 28 to thepressure line 30 for a longer interval than the interval during which it is connected to the vacuum line, if desired.

The desired modemay be selected by operating theswitch 31 that is connected to thecontrol box 32. This switch is shown positioned on the front panel of thecabinet 10 although a suitable foot control may be provided for actuating this switch. Avariable resistor 33 which may also be varied by a conventional foot control, is connected to themultivibrator 21 for control ling the frequency of the pulses in modes A and B. Mul'tivibrator 21 supplies electrical pulses for triggering flip-flop 22 and thus controls the frequency of the pulses produced by this flip-flop. Thevariable resistor 33 may also be provided with a foot control although it is shown as being controlled by the knob 33a provided on the front panel of the cabinet.

Theline 28 is connected to the fitting 280 which is attached to the front panel of the cabinet. This fitting is of the quick disconnect Luer type so that the line or tube 281; provided between it and thevacuum control device 34 may be readily disconnected therefrom. Thevacuum control device 34 which is shown in detail in FIG. 4, is provided with a T-connection 35 having twoarms 35a and 35b andline 28b is connected to arm 35a.Arm 35b is connected to line 36 which may be connected either to theinlet 37 orinlet 38 of thecontrol device 34 for purposes which will be described more fully hereinafter. Thecontrol device 34 is provided with apiston 39 of plastic that is slidable in thecylinder 40 and theports 37 and 38 lead into this cylinder, oneport 37 leading in below thepiston 39 and theother port 38 leading in at the top end thereof, and the purpose of this will also be described hereinafter.

v Apiston rod 41 which is also plastic is attached to thepiston 39 and extends into asmall cavity 42 into which thesmall tube 43 also extends. This end of thetube 43 is carefully lapped and polished and provides a seat for the end ofrod 41. Thus the lapped and polished end oftube 43 is alternately opened and closed by the end of thepiston rod 41 as thepiston 39 is moved back and forth during the operation of this device. The Luer type fitting 44 is attached to thecontrol device 34 and provides a connection between thesmall cavity 42 and thecylinder 45 which may be of 5 cc. capacity calibrated in one-tenth cc. increments to measure the vitreous or other material removed from the eye of the patient. Thestandpipe 45a incylinder 45 is connected by theline 46 to the top of thewaste overflow bottle 47. Thebottle 47 is also connected to thevacuum line 48 so that vacuum is provided therein.

Thevacuum control device 34 is also provided with anextension neck 49 and thesmall tube 43 which has an outer diameter of 0.6 mm., is concentric with theextension neck 49.Tube 43 extends outward beyondextension 49 so that asmall debris tube 50 is attached to the projecting part of thesmall tube 43. Thetube 50 is positioned inside of thetube 51 and this latter tube is attached to theprojection 49 of thedevice 34. Thetubes 50 and 51 are attached to a cutting and debris extracting device such as indicated at 52 which may be either of the type indicated at 53 shown in FIGS. 5 to 11 or of the type indicated at 54 shown in FIGS. 12 to 15. On the other hand a high frequencyelectric cutting device 55 such as shown in FIGS. 16 to 18 may be con-' sive, is provided with ahousing 56 which also functions as a handle and which has atubular projection 57 at one end thereof. Theplastic tube 51 is attached toprojection 57 so that alternate air and suction pulses according to either mode A or mode B are provided on the inside of this housing to operate thepiston 58 which is slidably positioned in thehousing 56.Piston 58 is made of fluorocarbon plastic and one end thereof is indented to receive'the nut 59 which engages the enlarged threaded portion 61 of the debris tube. The portion of the debris tube extends out of the piston and is inserted into the small hose orline 50 through which the debris is exhausted from the smallstainless steel tube 62.

Thepiston 58 is provided with aflag 63 which projects from one end thereof and slides inslot 63b which is provided to thecap 64. This flag keeps the piston from rotating with respect to the cap. Thecap 64 is provided with aknob 65 that is received by theslot 66 of thehousing 56 when this cap is attached to the housing. Thus, theflag 63 serves to orient thepiston 58 with respect to thecap 64 and theknob 65 serves to orient thecap 64 with respect to thehousing 56. The

purpose of this will be described hereinafter. Thecap 64 is provided with four radially extendingholes 67 which are adapted to be aligned with corresponding holes in thehousing 56 to provide venting of the inside of the housing during operation of this device. Thus, by providing four such holes it is not possible for the operator of this device to cover all of the holes simultaneously during use of this device so as to interfere with the operation thereof. Suitable threaded holes 68 are provided in thecap 64 and thescrews 69 are threaded into these holes through suitable apertures in thehousing 56 when the cap is assembled with the housing.

Atubular extension 70 is provided to the outside end of thecap 64 for receiving thestainless steel tube 71. The outer end of the tube orsleeve 71 is tapered and sharpened at 72 as shown in FIG. 10. The outer end of thesleeve 71 is also provided withslots 73 so that the opposite sections of this outer end may be slightly bent towards each other. Thus thesharp cutting edge 72 of the sleeve provides sharp shearing action with the sides of theholes 74 which are provided in theinner sleeve 62. This shearing action takes place as the inner sleeve is moved inward with respect to theouter sleeve 71 by thepiston 58 so that thesharp edge 72 sweeps across theholes 74 and severs any vitreous sucked into theholes 74. The end of thetube 62 is welded and ground as shown at 62b to close the end of the tube at this point and give this end a rounded configuration.

It will be noted that theslots 73 are aligned with the ribs oftubes 62 between theholes 74 and this alignment is maintained by theflag 63 which is slidable in therecess 63b of thecap 64 when thepiston 58 moves back and forth in the housing by the compressed air and suction pulses supplied to the cylinder and piston through thetube 51. Suction is supplied to theinner sleeve 62 through thetube 50 so that debris cut from the inside of the eye is exhausted through theholes 74 formed in thesleeve 62 and through this sleeve andtube 50.

A modified form of the pull-type cutting device is shown in FIG. 11 in which thetube 710 corresponds to thetube 71 of FIG. and the inner sleeve 62a corresponds to thesleeve 62 of FIG. 10. The device shown in FIG. 11 is provided with a triangular shaped cutting hole 74a through which material to be removed is sucked into the sleeve 62a and this material is severed by the sharp cutting edge of the outer sleeve 71a. A slot 73a is provided to the sleeve 71a so that the end portion of this sleeve may be slightly compressed to provide a tight fit between it and the sleeve 62a and facilitate the cutting of the material drawn into the tube 62a when this tube is moved into sleeve 71a and desired shearing action is obtained between thesharp cutting edges 72a and 74a.-

Another form of this device which is the push type cutting embodiment, is shown in FIGS. 12, 13, 14 and 15. Certain parts of this device provided in thehousing 76 are the same as corresponding parts provided in thehousing 56 of the pull type shown in FIG. 5. The device shown in FIGS. 12 through 15, inclusive, differs from that shown in FIGS. 5 to 11, inclusive, in that theouter sleeve 75 which is fixedly attached to thecap 64 is provided with aninner sleeve 77 which has theend 79 thereof tapered and honed to a sharp cutting edge. Theouter sleeve 75 is provided with an opening at the outer end portion thereof which is tapered and honed to a sharp edge so that when theinner sleeve 77 is moved outward thesesharp cutting edges 78 and 79 cooperate to shear off any vitreous or other material that has been sucked into the sleeve. In order to produce this desired shearing action theinner sleeve 77 is provided with aslot 80 so that the end portion of this inner sleeve is expanded slightly and provides a close fit between it and the inner wall of theouter sleeve 75.

Thedevice 55 shown in FIGS. 16, I7 and 18 is an example of a cutting device in which high frequency electric current is supplied to a self-cleaning electrode. This device is provided with atubular housing 81 having an air andsuction inlet member 82 attached to the side thereof. One end of the air andsuction line 83 is attached to theinlet member 82 and the other end is attached to the fitting 28a provided to thecabinet 10 shown in FIG. 1 after theother line 28b is detached from this fitting. Air and suction pulses according to mode A or B are supplied to the inside of thedevice 55 through theinlet member 82 and thehole 84 aligned therewith which communicates with the inside of thetubular housing 81 through theplug 85. This plug is of insulation material and it is attached to the end of thetubular housing 81 by suitable bayonet-type attaching means. Highfrequency coupling member 86 is attached to the plug and this member is of insulating material so that theelectrode 87 positioned therein is insulated from the tubular housing. Theelectrode 87 is connected to theflexible conductor 88 which is of conventional braided type and a suitable source of high frequency of conventional design is connected to theelectrode 87 by a coaxial cable of predetermined impedance. One end of the braidedcopper wire conductor 88 is soldered to the small bolt or screw 89 and the other end is soldered into thesleeve 91. One end of thecoil spring 90 abuts the inner end of theplug 85 and the other end of the coil spring abuts theinsulation sleeve 92 that is positioned in thetubular housing 81. The other end of this insulation sleeve abuts the shoulder provided inside of thetubular housing 81 as shown in FIG. 17. Thescrew 89 is inserted into thepiston 93 of fluorocarbon plastic material.Piston 93 is slidable inside of thehousing 81 and it is moved through a short stroke of about 1 /2 mm. by the compressed air and suction pulses supplied thereto through thepneumatic line 83. Thepiston 93 is held on thescrew 89 by thenut 94 and it is attached to anothernut 95 which functions as a chuck for theelectrode wire 96.Electrode wire 96 is provided with asmall knob 97 at the end thereof and this knob is pressed against the end of thescrew 89 when thechuck 95 is attached to the screw.Electrode wire 96 passes through the central hole provided in theinsulation plug 98.Plug 98 is provided withthreads 99 and is attached thereby to thetubular housing 81. Anotherplug 100 is attached by threads 101 to theplug 98 and a shortplastic tube 102 is attached in the central hole provided to plug 100. One end of theinsulation sleeve 103, which is of quartz coated with a plastic such as Teflon, is inserted into theplastic tube 102 up to theconstricted part 104. Theplastic tube 102 is provided with theconstricted portion 104 to increase the flexibility thereof so that thetube 103 may be moved slightly in the direction of the arrows shown in FIG. 16 by flexing thetube 102 at thearea 104. Theelectrode wire 96 passes through thetube 103 and during the back and forth movement of the piston 93 a small portion of theelectrode wire 96 is exposed at the free end of thesleeve 103. The amount of this exposure may be controlled by adjusting theplug 100 with respect to theplug 98. However, as theelectrode wire 96 is moved back and forth the outer end thereof is cleaned by the outer end of thesleeve 103 so that material such as coagulated protein adhering to theelectrode wire 96 is scraped therefrom by the end of thesleeve 103.

In FIG. 19 there is shown an arrangement for automatically injecting normal saline solution or other liquid into the eye of the patient as material is removed therefrom. This arrangement includes an L or book shapedconduit 105 which has a diameter of 0.6 mm. or less and which is hooked into the eye of the patient so that it is self retaining. Theconduit 105 is connected by theplastic tube 106 to abottle 107 of saline solution which is supported well above the patient so that the solution feeds into the patients eye as vitreous or other material is removed therefrom to replace such removed material and maintain a predetermined pressure.Conduit 105 is designed to fit snugly against the eyeball with-a low profile so that it is out of the way of viewing and possible snagging of objects. This conduit could be made of various materials such as metal, plastic, fused quartz or glass.

While we have shown and described a preferred form of the invention, it will be apparent that the invention is capable of modification and variation from the form shown, so that the scope thereof should be limited only by the proper scope of the claims appended hereto.

What we claim is:

1. In an apparatus for intraocular surgery such as cutting or severing of undesired material within the eyeball of a patient, the combination comprising a cutting electrode of very small diameter, an insulated tubular member having an open outer end in communication with an electrode-receiving bore extending longitudinally of said member for slidably and snugly receiving said cutting electrode, a source of electric current, means connecting said source to said cutting electrode and means reciprocating said cutting electrode in said tubular member so that the outer end of said cutting electrode intermittently projects from and recedes within said outer end of said tubular member during the cutting whereby coagulated material adhering to said electrode is removed therefrom by a scraping action of said outer end of said tubular member.

2. In an apparatus for intraocular surgery such as cutting or severing of undesired material within the eyeball of a patient, the combination as set forth inclaim 1, further characterized in that said connecting means comprises a transmission line having a predetermined impedance and a matching impedance connecting said cutting electrode to said transmission line.

3. ln an apparatus for intraocular surgery such as cutting or severing of undesired material within the eyeball ofa patient, the combination as set forth inclaim 1, further characterized in that said insulated tubular memher is connected to a handle by a flexible member.

4. In an apparatus for intraocular surgery such as cutting or severing of undesired material within the eyeball ofa patient, the combination as set forth in claim 3, further characterized in that said moving means comprises a piston slidable in said handle, means attaching said electrode to said piston, and pneumatic means reciprocating said piston.

5. In an apparatus for intraocular surgery such as cutting or severing of undesired material within the eyeball ofa patient, the combination as set forth in claim 3, further comprising means adjusting said tubular member with respect to said handle so that the excursion of the end of said electrode from said tubular member may be adjusted.

6. A lightweight device for intraocular surgery such as cutting or severing of undesired material within the eyeball of the patient, the combination comprising an electrode of small diameter, a tubular handle, means supporting said electrode projecting from one end of said handle, said means including a small sleeve, said electrode being slidable in said sleeve, actuating means inside of said handle attached to said electrode, pneumatic means connected to said handle providing alternately compressed air and vacuum for moving said last means through short strokes so that said electrode is moved through said short strokes inside of said sleeve and the outer end of said electrode is alternately projected from the outer end of said sleeve, a source of high frequency electric current, means connecting said source to said electrode to energize said electrode for the cutting and severing operation when said outer end of said electrode is periodically exposed at the end of said sleeve.

7. A lightweight device as set forth in claim 6, further characterized in that said sleeve is adjustable with respect to said tubular handle so that the length of said electrode that is projected from said sleeve may be adjusted.

8. A lightweightdevice as set forth in claim 6, further characterized in that said actuating means comprises a member slidable in said handle and said connecting means includes a chuck carried by said member for receiving an end of said electrode inside of said handle.

9. A lightweight device as set forth in claim 6, further comprising a valve for connecting said pneumatic means to said handle and means controlling said valve for alternately providing said compressed air and vacuum.

10. A lightweight device as set forth inclaim 9, further characterized in that said valve controlling means includes an electromagnetic device and means energizing said device at a predetermined rate.

11. A lightweight device as set forth inclaim 10, further comprising means for varying said predetermined rate at which said electromagnetic device is energized. =l =l =l=

Claims (11)

1. In an apparatus for intraocular surgery such as cutting or severing of undesired material within the eyeball of a patient, the combination comprising a cutting electrode of very small diameter, an insulated tubular member having an open outer end in communication with an electrode-receiving bore extending longitudinally of said member for slidably and snugly receiving said cutting electrode, a source of electric current, means connecting said source to said cutting electrode and means reciprocating said cutting electrode in said tubular member so that the outer end of said cutting electrode intermittently projects from and recedes within said outer end of said tubular member during the cutting whereby coagulated material adhering to said electrode is removed therefrom by a scraping action of said outer end of said tubular member.

2. In an apparatus for intraocular surgery such as cutting or severing of undesired material within the eyeball of a patient, the combination as set forth in claim 1, further characterized in that said connecting means comprises a transmission line having a predetermined impedance and a matching impedance connecting said cutting electrode to said transmission line.

3. In an apparatus for intraocular surgery such as cutting or severing of undesired material within the eyeball of a patient, the combination as set forth in claim 1, further characterized in that said insulated tubular member is connected to a handle by a flexible member.

4. In an apparatus for intraocular surgery such as cutting or severing of undesired material within the eyeball of a patient, the combination as set forth in claim 3, further characterized in that said moving means comprises a piston slidable in said handle, means attaching said electrode to said piston, and pneumatic means reciprocating said piston.

5. In an apparatus for intraocular surgery such as cutting or severing of undesired material within the eyeball of a patient, the combination as set forth in claim 3, further comprising means adjusting said tubular member with respect to said handle so that the excursion of the end of said electrode from said tubular member may be adjusted.

6. A lightweight device for intraocular surgery such as cutting or severing of undesired material within the eyeball of the patient, the combination comprising an electrode of small diameter, a tubular handle, means supporting said electrode projecting from one end of said handle, said means including a small sleeve, said electrode being slidable in said sleeve, actuating means inside of said handle attached to said electrode, pneumatic means connected to said handle providing alternately compressed air and vacuum for moving said last means through short strokes so that said electrode is moved through said short strokes inside of said sleeve and the outer end of said electrode is alternately projected from the outer end of said sleeve, a source of high frequency electric current, means connecting said source to said electrode to energize said electrode for the cutting and severing operation when said outer end of said electrode is periodically exposed at the end of said sleeve.

7. A lightweight device as set forth in claim 6, further characterized in that said sleeve is adjustable with respect to said tubular handle so that the length of said electrode that is projected from said sleeve may be adjusted.

8. A lightweight device as set forth in claim 6, further characterized in that said actuating means comprises a member slidable in said handle and said connecting means includes a chuck carried by said member for receiving an end of said electrode inside of said handle.

9. A lightweight device as set forth in claim 6, further comprising a valve for connecting said pneumatic means to said handle and means controlling said valve for alternately providing said compressed air and vacuum.

10. A lightweight device as set forth in claim 9, further characterized in that said valve controlling means includes an electromagnetic device and means energizing said device at a predetermined rate.

11. A lightweight device as set forth in claim 10, further comprising means for varying said predetermined rate at which said electromagnetic device is energized.

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