CA2060758A1 - Surgical cutting instrument - Google Patents
Surgical cutting instrumentInfo
- Publication number
- CA2060758A1 CA2060758A1 CA002060758A CA2060758A CA2060758A1 CA 2060758 A1 CA2060758 A1 CA 2060758A1 CA 002060758 A CA002060758 A CA 002060758A CA 2060758 A CA2060758 A CA 2060758A CA 2060758 A1 CA2060758 A1 CA 2060758A1
- Authority
- CA
- Canada
- Prior art keywords
- cutting
- recited
- teeth
- inner member
- cutting edge
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Abandoned
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/32—Surgical cutting instruments
- A61B17/320016—Endoscopic cutting instruments, e.g. arthroscopes, resectoscopes
- A61B17/32002—Endoscopic cutting instruments, e.g. arthroscopes, resectoscopes with continuously rotating, oscillating or reciprocating cutting instruments
Abstract
ABSTRACT
The cutting strength of a rotary surgical cutting instrument is increased by an on-axis bearing contact between the distal end of its rotatable inner member and the interior surface of its outer member. The outer member is provided with a distal cutting aperture angularly oriented to the rotation axis and circumscribed by an oval outer cutting edge. The inner member has two symmetrical rows of straight-sided triangular cutting teeth positioned to cooperate with the outer cutting edge to shear tissue, including bone, disposed in the cutting aperture. A
clearance gap between the inner and outer members narrows in width in the region between the teeth and the aperture to prevent severed tissue from lodging between the inner and outer members. The height of the cutting teeth is at least 50% of their width, and 15%
to 22% of the outer diameter of the inner member. The straight sides of the teeth converge to crests disposed in a first common longitudinal plane. The teeth are separated by roots disposed in a second plane parallel to the first plane but disposed closer than the first plane to the rotation axis.
The cutting strength of a rotary surgical cutting instrument is increased by an on-axis bearing contact between the distal end of its rotatable inner member and the interior surface of its outer member. The outer member is provided with a distal cutting aperture angularly oriented to the rotation axis and circumscribed by an oval outer cutting edge. The inner member has two symmetrical rows of straight-sided triangular cutting teeth positioned to cooperate with the outer cutting edge to shear tissue, including bone, disposed in the cutting aperture. A
clearance gap between the inner and outer members narrows in width in the region between the teeth and the aperture to prevent severed tissue from lodging between the inner and outer members. The height of the cutting teeth is at least 50% of their width, and 15%
to 22% of the outer diameter of the inner member. The straight sides of the teeth converge to crests disposed in a first common longitudinal plane. The teeth are separated by roots disposed in a second plane parallel to the first plane but disposed closer than the first plane to the rotation axis.
Description
2 Q ~
BACKGROUND OF THE INVENTION
1 Field of The Invention 2 The present invention relates to surgical cutting instruments 3 and, more specifically, to surgical cutting instruments formed of 4 coaxial inner and outer members and having teeth for cutting tissue, including bone. The invention has particular utility in 6 rotatably driven cutting instruments used in arthroscopic surgery.
7 Description Of The Prior Art 8 It is known in the prior art to provide surgical cutting 9 instruments comprising an outer sleeve with a cutting aperture and a toothed inner tube rotatably mounted within the outer sleeve, 11 permitting the teeth to rotate past the cutting aperture to cut 12 tissue received therei~. Examples of cutting instrum~nts of this 13 type are disclosed in U.S. Patent Nos. 4,368,734 (Banko) and 14 3,618,611 (Urban). Such instruments possess numerous disadvantages including the relative ineffectiveness o~ the concaYely curved 16 sides of their cutting t~ath in cutting tissue. Speci~ically, when 17 the inner tube is rotated relative to the outer sleeve, the crests 18 of the teeth pierce tissue positioned in the cutting aperture and, 19 as the concave sides of the teeth continue to pass through the tissue, the tissue collects or bunches up in the curved spaces 21 between the teeth. Consequently, the concave-sided teeth cut 22 tissue in a tearing or digging action, rather than with a clean 23 shear cut, the result often being trauma to tissue and the need for 2~7~
1 relatively long cutting times and hig~ cutting forces to cut ~ven 2 small tissue quantities. Additionally, the height o~ typical 3 cllrved cutting teeth is very small in relation to their width and 4 to the diameter of the inner tube, and such shallow teeth are capable of cutting only small increments of tissue for each 6 rotation past the cutting aperture. A further drawback to cutting 7 instruments having teeth with concave sides is that the teeth are 8 formed by overlapping radial machine cuts in the inner tube such 9 that the distance between the origins of the radii of the machine cuts is less than the diameter of their corresponding circles. The 11 overlapping radial machine cuts remove substantial quantities of 12 material from the inner tube, resulting in a substantial reduction 13 in the tube strength. The concavely curved cutting teeth, 14 there~ore, generally lack the structural integrity required to apply high cutting forces required cut bone, or to tolerate impact 16 forces arising from incidental contact with other instruments at 17 the surgical site.
18Other surgical cutting instruments of the general type 19 described but having straight-sided cutting teeth are disclosed in 20U.S. patent No. 2,721,555 (Jenny) and in an article by Aksenova et 21 al entitled "New Biopsy Instruments", published in Biomedical 22 Engineering (Vol. 13, No. 4). However, these instruments are 23 generally limited to cutting small fragments of easily penetrable 24 tissue, such as skin and other delicate tissue, due to the cutting teeth being formed as very fine serration~. More particularly, the 26 height of the straight-sided cutting teeth is typically very small 2 0 ~
1 in relation to their width and to the diameter of the inner tube 2 and, therefore, the effective cutting length of the cutting edge 3 presented by the straight-sided cutting teeth is only slightly 4 larger than the axial length of khe inner member segment along which the teeth are defined. Accordingly, the straight-sided teeth 6 generally cut relatively small amounts of tissue for each rotation 7 past the cutting aperture, require relatively long cutting times to 8 cut tissue, and are defined in a relatively weak structure so as to 9 be precluded from use in surgical procedures necessitating high cutting forces that might break or damage the relatively fragile 11 inner member.
12 The structural configuration, limited cutting effectiveness 13 and minimal strength of presently available curved and straight-14 sided cutting teeth typically limit instruments utilizing these cutting teeth to specific cutting functions and types o~ tissue.
16 Such instruments cannot be employed, for example, ts perform 17 multiple, diverse cutting functions, such as resecting, trimming, 18 side cutting, whiskering, burring and the like, on diverse types of 19 tissue including relatively elastic tissue as well a~ relatively hard tissue, such as hone. The functional limitations of such 21 instruments make it necessary to utilize many specialized cutting 22 instruments in surgical procedures, such as arthrosopy, involving 23 multiple, diverse cutting operations on different types of tissue, 24 thereby adding signi~icantly to the time and complexity of these procedu~es.
26 A further drawback shared by surgical cutting instruments of 2~75~
1 the type described is that a gap is usually maintained between the 2 outer sleeve and the inner tube to permit the inner tube to freely 3 rotate within the outer sleeve without friction and thP attendant 4 and potentially damaging heat. This gap, however, is typically wide enough adjacent the cutting teeth for tissue to be drawn 6 therein. Tissue is thusly caught between the outer sleeve and the 7 rotating inner tube and, when the inner tube is rotated at high 8 speeds, the tissue becomes wrapped around the inn~r tube. When 9 this occurs, rotation of the inner tube is impeded and sometimes totally blocked, requiring time and attention to be diverted from 11 the surgical procedure to ~ree the caught tissue. Moreover, the 12 ', gap between the inner and outer tubes tends to promote misalignment 13 between these tubes when cutting forces are imposed between them.
14 Since there is no structure in the gap to preserve positional stability of the inner tube, the resulting misalignment impairs the 16 cutting efficiency and effectiveness of the surgical instrument.
18 Accordingly, it is a primary ob j ect of the present invention 19 to overcome the above-mentioned disadvantages associated with prior art cutting instrument~ having curved or straight-sided cutting 21 teeth~
22 It is another object of the invention to provide a surgical 23 cutting instrument having cutting te~th capable of performing 24 diverse cutting operations on different types of tissu~, including bone.
2 ~
1 A further object of the invention is to provide a surgical 2 cutting instrument having cutting teeth formed in a rotatable tube 3 capable of applying large cutting forces.
4 An additional object of the invention is to provide a surgical cutting instrument having a rotatable inner member carrying cutting 6 teeth capable of cutting relatively large quantities of tissue 7 during each rotation of the inner member.
8 Yet another object of the invention is to provide a surgical 9 cutting instrument of the type described wherein the e~fective cutting length provided by cutting teeth is signi~icantly longer 11 then in prior art instruments.
12 It is also an object of the in~ention to prevent misalignment 13 between the toothed rotating inner member and the outer tubular 14 member in a surgical cutting instrument of the type described.
A still fur~her ob~ect o~ the invention is to prevent tissue 16 from being trapped or jammed between a toothed cutting edge on 17 rotating inner member and a cutting edge on an apertured outer 18 tubular member coaxially receiving the inner member.
19 Among the advantages of the surgical cuttiny instrument of the present invention over the prior art are: reduced time required to 21 surgically cut tissue; increased strength of the cutting tePth 22 resulting from minimizing the quantity of material removed ~rom the 23 inner member in forming teeth edges; minimization of damaging 24 frictional heat from high speed rotation of the inner mamber within the outer member; and elimination of the need for multiple 26 specialized cutting instruments to ef~ect different types of cuts 2~7~
1 in certain surgical procedures, in particular, arthroscopic 2 procedures.
3 These and other objects, benefit~ and advantages are achieved 4 with the surgical cutting instrument of the present invention as S characterized by an o~lter tubular member including a proximal end 6 and a distal end ~lith a cutting aperture for receiving tissue, and 7 a coaxially received inner tubular member including a proximal end 8 and a toothed distal end for cutting tissue. The inner member 9 distal end includes a distal cutting edge segment angularly joined to toothed cutting edge segments disposed symmetrically along 11 opposite sides of the inner member. The distal end of the inner 12 member contacts the inner surface of the outer mPmber distal end at 13 a single bearing contact point on the rotation axis to positionally 14 stabilize and support the inner member and prevent misalignments between the members. Each toothed cutting edge segment includes a 16 plurality of longitudinally aligned cutting teeth extending 17 proximally from the distal cutting edge segment. The cutting teeth 18 are defined by straight sides converging at coplanar crests, and l9 joined by coplanar roots, the plane of the roots being parallel to the plane of the crests but located closer to the longitudinal axis 21 (i.e., the rotation axis) of the inner member. The location of 22 these planes is such that at least 80% of the height of each 23 cutting tooth extends into the semi-cylindrical side oP the inner 24 member from which most of the material has been removed to form the teeth. In addition, the height o~ the teeth is at least 50% of 26 their width and on the order of 15% to 22% of the inner member 1 diameter. Respective concave transition segments join the toothed 2 cutting edge segments to the distal leading cutting edge segment.
3 Respective rearward concave sides of the most proximal teeth serve 4 as transitions to inclined edge segments extending from a centered proximal edge segment. The cutting aperture in the outer member is 6 circumscribed by a cutting edge ~ormed by cuttin~ a section in a 7 plane positioned angularly with the central longitudinal axis of 8 the outer member. A clearance gap between the inner and outer 9 members is interrupted only by the single bearing contact point.
The gap has a predetermined width but tapers to a relatively narrow 11 width between the edge of the cutting aperture and th~ cutting 12 teeth to prPvent tissue from being drawn between the cutting 13 aperture and the teeth and becoming wrapped around th inner 14 member.
Other objects and advantages of the present invention will 16 become apparent from the following description of the preferred 17 embodiments taken in conjunction with the accompanying drawings.
19 Fig. 1 is a broken, exploded side view, partly in section, of the surgical cutting instrument according to the present invention.
21 Fig. 2 is a broken side view, partly in section, of the 22 surgi~al cutting instrument of Fig. 1 with a handpiece drive unit.
23 Fi~. 3 is a broken side view, partly in section, of the distal 24 end of the outer tubular member of the surgical cutting instrument o~ ~ig. 1 ~a7~
1 Fig. 4 is a view in sec~ion of the outer tubular member taken 2 along line 4-4 of Fig. 3.
3 Fig. 5 is a broken side view of the distal end of the inner 4 tubular member of the surgical cutting instrument of FigO 1.
Fig. 6 is a broken, ~op view of the distal end of the inner 6 tubular member of the inner tubular member of the surgical cutting 7 instrument of Fig. 1.
8 Fig. 7 is a broken side YieW of the distal end of an 9 alternative embodiment of an inner tubular member of the surgical cutting instrument according to the present invention.
11 Fig. 8 is a broken side view of the distal end of the surgical 12 cutting instrument according to the present invention showing the 13 inner tubular member being rotated with respect to the outer 14 tubular member.
Fig. 9 is a view in section of the surgical cutting instrument 16 taken along line 9-9 of Fig. 8.
17 Fig. 10 is a view in section of the surgical cutting 18 instrument taken along line 10-10 of Fig. 8.
As shown in Figs~ 1 and 2, a surgical cutting instrument 12 21 according to the present invention includes an elongate outer 22 tubular member 14 and an elongate inner tubular member 16 rotatably 23 disposed within the outer member 1~. The surgical cutting 24 instrument 12 is particularly configured to be received in and driven by a handpiece drive unit 18 having a distal end shown in 20~a~
1 Fig. 2. Handpiece drive unit 18 is the handpiece of the Concept 2 Model 9950 INTRA-ARC Drive System, and reference is made thereto 3 for more specific detail relating to the structure and operation of 4 the handpiece. The handpiece drive unit 18 is described herein only to the extent required ~o understand the operation o~ the 6 surgical cutting instrument 12.
7 Handpiece drive unit 18 includes a yenerally cylindrical body8 20 having an enlarged forward end 22 sealed by a locking ring 24, 9 a longitudinally extending cylindrical bore having a rearward boresection (now shown) for housing a drive motor, an intermediate bore 11 section 26 receiving a drive shaft 28 rotatably driven by the drive 12 motor, a forward bore section 30 receiving the proximal end of the13 surgical cutting instrument 12, and an aspirating chamber 32 14 positioned between the intermediate bore section 26 and the forward bore section 30. The aspirating chamber 32 communicates with a 16 vacuum source (not shown) via suction channels 34 and 36 formed in17 the body 20. A plurality of push-button switches 38 are dispose~
18 on the handpiece drive unit 18 to control operation of the drive 19 motor.
Locking ring 24 includes an exposed forward-~acing surface, a 21 rearward-facing surface abutting the forward end 22 of body 20 and22 an annular lip 40 extending axially over a short len~th of the 23 forward end 22. A circular recess in the forward facing surface is24 disposed concentrically about a central aperture 42, and two arcuat~ channels are defin~d through the locking ring within the 26 recess ~qually spaced from a slot therein and dispos~d 2 ~
1 symmetrically about aperture 42. Each channel subtends 2 approximately 90 of arc at a constant radial distance from the 3 center of aperture 42. A disc-shaped spacer 44 is disposed in ~he 4 locking ring recess and has a central aperture aligned with the aperture 42. Spacer 4~ is secured via screws to body 20, the 6 screws passing ~hrough the two respective arcuate channels to 7 permit the locking ring 24 to be rotated relative to the spacer 44 8 and the body 20, limited by the arcuate lengths o~ the channels 9 (i.e., 90~). Spacer 44 also has a slot extending axially therethrough to a prescribed radial depth from the central 11 aperture, such that when the spac~r slok is rotatably aligned with 12 ~- the slot in the locking ring 24 and with a slot 46 in the forward 13 bore section 30, a locator stub 48 on the proximal end of the 14 surgical cutting instrument 12 can freely pass into and out of the handpiece drive unit 18.
16 The rearward-facing surface of the locking ring 24 includes an 17 arcuate ramp surface extending approximately 140~ from the slot 18 along the outer edge of the aperture ~2 to serve as a camming 19 surface for inserting the proximal end of the surgical cutting instrument 12 int~ the handpiece drive unit 18. In one extreme 21 rotational position of the locking ring 24, the slot in the locking 22 ring 24 is aligned with the slot in the spacer ~4 and with the slot 23 46 in the forward bore section 30, whereby the surgical cutting 24 instrument 12 can be inserted through the locking ring 24 sufficiantly far that an open end thereof slides over the forward 26 end of the drive shaft ~8, and the locator stuh 48 is disposed in ri ~
1 slot 46 with just a small portion of the stub projecting partially 2 into the locking ring slot. If the locking ring 24 is then rotated 3 90 to its other extreme position, the camming surface gradually 4 forces the locator stub 48, and with it the surgical cutting instrument 12, rearwardly to produce positive engagement with the 6 drive shaft 28. The two extreme positions of the locking ring 24 7 are maintained by a detent ball 50 and a spring 52 located in a 8 recess in the forward end 2~ of the body 20. The detent ball and 9 spring 52 cooperate with two dimples formed at 90 spaced locations 10 in the rearward-facing surface of the locking ring 24 to provide 11 stops at the two extreme rotational positions o~ the locking ring.
12 In order to remove the surgical cutting instrument 12 from the 13 handpiece drive unit 18, the locking ring 24 is rotated 90' in the 14 opposite direction to its initial extreme position. When the slot 15 in the locking ring 24 becomes aligned with the spacer slot 44 and 16 the slot 46, the surgical cutting instrument 12 can be easily 17 removed from the handpiece drive unit.
18 A hub 54 is mounted on a proximal end 56 of the outer tubular 1~ member 14, the hub 54 being made o~ plastic or metal and havlng a 20 generally cylindrical configuration with the locator stub 48 21 extending radially therefrom to be received in the slots in the 22 handpiece drive unit 18 as described above. Hub 54 includes a 23 cylindrical recess 58 defined in its proximal end in communication 24 with a distally extending central bore 60 for receiving the 25 proximal end 56 of the outer member 14. A spring 62 is disposed in 26 recess 58 and includes four equally spaced arms extending radially 2 ~
1 from a central aperture 64 along the bottom of recess 58 and bent 2 to extend proximally along the cylindrical side wall of th~ recess.
3 One pair 66 of opposing spring arms has curved inwardly bent ends 4 to engage the inner member 14, while the other pair of opposing spring arms 68 has square outwardly bent ends to hold the spring 62 6 in place in the recess 58.
7 A hub 70 is secured to the proximal end 72 of the inner 8 tubular member 16 and has a bevelled front lip 74 received in 9 recess 58 in hub 54 of outer member 14 so as to be held in place by spring arms 66. The proximal end 72 of inter tubular member 16 is 11 secured in and extends through an axial bore in hub 70 to 12 communicate with a passage 76 extending diametrically through hub 13 70 to be disposed in the aspirating chamber 32 in handpiece drive 14 unit 18. A pair of radial ribs 78 is positioned rearwardly of the passage 76 and extend longitudinally to a chamfered lip 80 carrying 16 a rearwardly projecting driven tang 82 adapted to be received in 17 drive shaft 28. A sleeve 84 is telescopically mounted over ribs 78 18 and drive tang 82, and is spring biased away from lip 80. ~s 19 illustrated in Fig. 2, wherein sleeve 84 is not shown, inner member 16 is rotatably driven within the outer member 14 by drive shaft 28 21 engaging the driven tang 82, while suction is produced in the inner 22 member 16 via the channels 34 and 36 communicating with the vacuum 23 source and passage 76. Although the surgical cutting instrument of 24 the present invention is shown and described for use in the Concept 2S INTRA-ARC system, it will be appreciated that the surgical cutting 26 instrument of the present invention can have any de~ired hub 1 configuration to be utilized with any drive system or handpiece 2 capable of rotating an elongate inner tubular member within an 3 elongate outer tubular member to cut or otherwise engage bodily 4 tissue at the distal end.
The outer tubular member ~4 is preferably made of a length of 6 stainless steel tubing having the proximal end 56 adhesively 7 secured in bore 60 of hub 54, and a distal end 86 configured as a 8 segment of a hemisphere and having an aperture or opening 88 9 defined therein to form a cutting port or window. As shown in Figs. 3 and 4, orifice 88 is formed by taking a section through a 11 plane inclined at an angle of approximately 15 to the longitudinal 12 ~ axis Y of outer member 14 and intersecting that axis slightly 13 forward of distal end 86 of that member. Orifice 88 is thus 14 circumscribed by a flat edge 90 of generaily elliptical configuration. The width of edge 90 in determined by the thickn~ss 16 of tubular member 14 in the inclined section plane. Edge 90 17 thereby defines a sharp cutting edge corner 98 at its intersection 18 with the inner surface of outer member i4. The cutting edge corner 19 98 is thus contained in a plane disposed at the acut~ section angle with central longitudinal axis Y of outer tubular member 14.
21 The inner tubular member 16 is preferably formed of length of 22 stainless steel cylindrical tubing having its proximal end 72 23 adhesively secured in hub 70. The distal end 100 of member 16 is 24 in the ~orm of a segment of a hemisphere and includes a cutting edge 102 rotatable past cutting edge corner 98 on outer member 14 26 to engage and cut tissue positioned in aperture 88 when inner 1 member 16 is rotatably driven within the outer member 14 by drive 2 shaft 28~ ~s shown in Figs. 5 and 6, cutting edge 102 is formed by 3 cutting away part of the distal end of member 16 and includes a 4 distal segment 104 arcuately configured and joined at its ends to side segments 106 extending longitudinally along respective 6 opposite sides of the inner member 16. Distal edge segment 104 is 7 an exposed arcuate edge of distal end 100 and is displaced 8 laterally from the central longitudinal axis X of member 16 (i.e., 9 slightly above that axis as viewed in Fig. 5). The opposite ends of distal edge segment 104 are co-planar and taper and a proximal 11 direction toward axis X at an angle of approximately 15. Side 12 - edge segments 106 ext~nd from respective ends of distal edge 13 segment 104 and are each formed as a series of longitudinally 14 aligned cutting teeth including distal tooth 116, proximal tooth 118 and intermediate teeth 114, all of generally triangular 16 configuration. Each tooth 114, 116, 118 is laterally aligned with 17 a corresponding tooth on the opposite side edge segment 106. A
18 smooth concave transition 112 between the tapering distal edge 19 segment 104 and the most distal tooth 116 in each series has a radius of curvature significantly smaller than the height (i.e., 21 along the tube circumference) and width (i.e.l along the tube 22 length) of the adjacent most distal tooth 116. Each cutting tooth 23 114, 116, 118 is defined by straight forward and rearward sides 120 24 and 122, respectively, converging symmetrically at an angle A to a crest 124. All of crests 124 are disposed in a first common plane.
26 The forward and rearward sides of adjacent teeth similarly 1 intersect at respective roots 126 located in a second common plane.
2 The crest plane and root plane are parallel to one another and to 3 the axis X of inner member 16. The plane of roots 126 is disposed 4 closer to axis X than is the plane of crests 124 whereby at least 80% (and preferably 90% or more) o~ the height of the teeth are 6 disposed on the same hemispherical side of axis X from which 7 material has been cut away to form the teeth. With this 8 configuration the tubular inner member 16 is circumferentially 9 continuous at said crests over an arc in excess o~ 180. In addition, the height of the teeth is no less than 50~ of their 11 width between roots 126 and, preferably, is between 60% and 70% of 12 ; the width. The rearward side 128 of the most proximal tooth 118 is 13 arcuate and defined by a radius of curvature considerably larger 14 than the radius of curvature of distal transition segment 112.
Rearward side 128 merges smoothly into a straight forward-facing 16 edge segment 130 inclined at substantially the same angle from axis 17 X as the forward sides 120 of teeth 114. Segment 130 extends to a 18 proximal edge segment 132 joining the two side segments 106 and 19 disposed on the same side of axis X as distal segment 104.
As best illustrated, in Fig. 10, an annular clearance gap 134 21 is provided between the outer surface of the inner member 16 and 22 the inner surface of the outer member 14 to permit high speed 23 rotation of the inner member within the outer member without 24 frictional engagement and the resulting heat that might damage the cutting instrument 12. Gap 134 extends substantially the entire 26 length of outer and inner members 14 and 16; however, the gap 2~75~
1 clearance tapers to reduced width sections 136 extending 2 longitudinally along both side segments 106 of cutting edge 102 3 (i.e., in the region of the teeth 114, 116 and 118). The gap 4 clearance 134 also tapers to a contact point 138 at the facing distal ends of the outer and inner tubular members 14 and 16.
6 Specifically, the inner surface of the distal end of outer tubular 7 member 14 contacts the outer surface of distal end 100 of inner 8 tubular member 16, and the bearing contact point 138 resides on the 9 coaxially disposed central longitudinal axes X and Y (i.e., the axis of rotation).
11 Preferably, angle A formed by the sides of cutting tPeth 114, 12 '116 and 118, is in the range of 66' to 77; the height of the 13 cutting teeth 114, 116 and 118 measured as the distance between the 14 plane of crests 124 and the plane of roots 126, is in the range of 15% to ~2% of the outer diameter of inner member 16; edge segments 16 130 define an angle of 50 to 60 with respect to the central 17 longitudinal axis X of inner member 16; ~he longitudinal plane 18 containing rooks 126 is at or close to axis X, whereas the plane 19 containing the crests 124 is more remote from that axis, so that between 90% and 100% height of teeth 114, llS, 118 r~side on the 21 ~emi-cylindrical side of the axis toward which the teeth generally 22 point: the plane containing edge 90 and edge corner 98 on the outer 23 member 14 defines an angle of approximately 15 with respect to the 24 central longitudinal axis Y of the outer member; and the width of gap 134 is approximately .0005 inches and the width of th~ narrowed 26 width sections 136 is approximately .00025 inches.
2 ~
1 Although the side cutting edge segments 106 are depicted in 2 Fig. 5 as including five cutting teeth on each side, the exact 3 number of teeth can vary in accordance with the diameter of inner 4 member 16, there being fewer cutting teeth provided on smaller diameter inner members. As shown in Fig~ 7, a relatively small 6 diameter inner tubular member 216 includes four cutting teeth 214 7 on each side segment 206.
8 The relative proportions and configurations describPd herein 9 produce numerous advantages. The straight configuration for the forward and rearward facing tooth sides 120 and 122 strengthens the 11 cutting teeth 114, 116, 118 by minimizing the quantity of metal 12 material that must be removed from inner member 16 to form the 13 teeth. In addition, the straight tooth sides effect a shearing 14 action as opposed to tearing the tissue. The straight forward and rearward facing tooth sides are effective in cutting tissue, 16 including bone, for the entire height of the cutting teeth, and the 17 crest angle A provides effective shear cutting in both relatively 18 soft and hard tissue. The specified range of heights of the 19 cutting teeth relative to the outer diameter of the inner tubular member 16, and the range of tooth heights relative to tooth widths, 21 provides structurally strong cutting teeth. The strong cutting 22 teeth minimize tooth breakage and enable the teeth to shear large 23 quantities of tissue during each passage of a cutting edge side 24 region 106 past the aperture 88. The location of the plane containing roots 126 proximate the central longitudinal axis X of 26 the inner member 16 further increases the strength of the cutting 2 ~ ~ ~3 ri ~ ~3 1 end of member 16 by providing a larger structural support than i5 2 present when little or no part of the teeth project into the 3 semicylindrical region opposite the support structure for the 4 teeth. The angular orientations of the distal edge segment 104, concave transitions 112, arcuate segments 12~ and the forward-~ facing segments 130 are selected to further minimize the quantity 7 o~ metal material removed from the inner member 16 during machining 8 and, thereby, enhance the structural integrity of thak member. The 9 angular orientation of edge 90 and its corner 98 relative to axis Y of outer member 14 reduces the amount of material removed from 11 the outer member and thusly ~trengthens that member while providing 12 controlled, sequential cutting of tissue when one of the side edge 13 segments 106 is rotated past the cutting edge corner 98. The 14 distal contact point 138 supports and positionally stabilizes the inner tubular member 16 as it rotates in outer tubular member 14 to 16 prevent misalignment of the members at high rotation speeds.
17 Contact point 138 serves to further positionally stabiliæe the 18 inner member 16 when large cutting forces are imposed and, 19 therefore, permits hard tis~ue, such as bone, to be cut without deforming member 16. The reduced width sections 136 of the 21 clearance gap 134 prevent tissue from being drawn between the 22 members and becoming wrapped around the rotating inner member 16.
23 In operation, the surgical cuttinq instrument 12 is inserted 24 into handpiece drive unit 1~ in the manner described above and is positioned at the surgical site through a portal for arthroscopic 26 surgery. The speed and operation of the surgical cutting lg 2~7~
1 instrument 12 is controlled by switches 38, and the surgeon 2 advances the surgical cutting instrument 12 to position tissue, 3 such as bone and meniscus cartilage, within aperture 88 in outer 4 tubular member 14. As shown in Fig. 8, the inner member 16 is rotatably driven within the outer member 14, such that a portion of 6 the distal cutting edge segment 104 and one of the cutting edge 7 side segments sequ~ntially penetrate and cut tissue when rotated 8 past the cutting edge cornex 98. Severed tissue is aspirated 9 through the lumen of the inner tubular member 16 to exit the surgical instrument 12 via the passage 76 communicating with the 11 aspirating chamber 32 in the handpiece drive unit 18. The cutting 12 teeth 114, 116, 118 produce an aggressive cutting action in tissue, 13 including bone, and the converging forward and rearward facing 14 tooth sides 120 and 122 cut tissue in a shearing action rather than a tearing or digging type of cut. As shown in Fig. 9, the crPsts 16 126 of the straight-sided, triangular shaped teeth pierc and grip 17 tissue 140 positioned in the outer member aperture 88, and pull the 18 tissue into such opening as the inner member 16 rotates. The 19 forward and rearward facing sides 120 and 122 of the teeth continue to cut through the tissue 140 in a shearing action as the teeth 21 move across the opening 88. The surgical cuttiny instrument 12 22 possesses the ability to perform diverse cutting operations on both 23 so~t and hard tissue that would normally necessitate the use of 24 diverse, specialized ~utting blades. For example, the surgical cutting instrument 12 can be utilized as a ~ull radius resector, a 26 synovial r~sector, a trimmer, a meniscus cutter, a side cutter, a .5 ~
1 whisker, an arthroplasty burr, and the like, for cutting, shaping 2 and finishing bone surfaces as well as other types of tissue.
3 Having de~scribed a preferred e~bodiment of a new and improved 4 surgical cutting instrument constructed in accordance with the present invention, it is believed that other modifications, 6 variations and changes will be suggested to those skilled in the 7 art in view of the teachings set forth herein. It is therefore to 8 be understood that all such variations, modifications and changes 9 are believed to fall within the scope of the present invention as defined by the appended claims.
BACKGROUND OF THE INVENTION
1 Field of The Invention 2 The present invention relates to surgical cutting instruments 3 and, more specifically, to surgical cutting instruments formed of 4 coaxial inner and outer members and having teeth for cutting tissue, including bone. The invention has particular utility in 6 rotatably driven cutting instruments used in arthroscopic surgery.
7 Description Of The Prior Art 8 It is known in the prior art to provide surgical cutting 9 instruments comprising an outer sleeve with a cutting aperture and a toothed inner tube rotatably mounted within the outer sleeve, 11 permitting the teeth to rotate past the cutting aperture to cut 12 tissue received therei~. Examples of cutting instrum~nts of this 13 type are disclosed in U.S. Patent Nos. 4,368,734 (Banko) and 14 3,618,611 (Urban). Such instruments possess numerous disadvantages including the relative ineffectiveness o~ the concaYely curved 16 sides of their cutting t~ath in cutting tissue. Speci~ically, when 17 the inner tube is rotated relative to the outer sleeve, the crests 18 of the teeth pierce tissue positioned in the cutting aperture and, 19 as the concave sides of the teeth continue to pass through the tissue, the tissue collects or bunches up in the curved spaces 21 between the teeth. Consequently, the concave-sided teeth cut 22 tissue in a tearing or digging action, rather than with a clean 23 shear cut, the result often being trauma to tissue and the need for 2~7~
1 relatively long cutting times and hig~ cutting forces to cut ~ven 2 small tissue quantities. Additionally, the height o~ typical 3 cllrved cutting teeth is very small in relation to their width and 4 to the diameter of the inner tube, and such shallow teeth are capable of cutting only small increments of tissue for each 6 rotation past the cutting aperture. A further drawback to cutting 7 instruments having teeth with concave sides is that the teeth are 8 formed by overlapping radial machine cuts in the inner tube such 9 that the distance between the origins of the radii of the machine cuts is less than the diameter of their corresponding circles. The 11 overlapping radial machine cuts remove substantial quantities of 12 material from the inner tube, resulting in a substantial reduction 13 in the tube strength. The concavely curved cutting teeth, 14 there~ore, generally lack the structural integrity required to apply high cutting forces required cut bone, or to tolerate impact 16 forces arising from incidental contact with other instruments at 17 the surgical site.
18Other surgical cutting instruments of the general type 19 described but having straight-sided cutting teeth are disclosed in 20U.S. patent No. 2,721,555 (Jenny) and in an article by Aksenova et 21 al entitled "New Biopsy Instruments", published in Biomedical 22 Engineering (Vol. 13, No. 4). However, these instruments are 23 generally limited to cutting small fragments of easily penetrable 24 tissue, such as skin and other delicate tissue, due to the cutting teeth being formed as very fine serration~. More particularly, the 26 height of the straight-sided cutting teeth is typically very small 2 0 ~
1 in relation to their width and to the diameter of the inner tube 2 and, therefore, the effective cutting length of the cutting edge 3 presented by the straight-sided cutting teeth is only slightly 4 larger than the axial length of khe inner member segment along which the teeth are defined. Accordingly, the straight-sided teeth 6 generally cut relatively small amounts of tissue for each rotation 7 past the cutting aperture, require relatively long cutting times to 8 cut tissue, and are defined in a relatively weak structure so as to 9 be precluded from use in surgical procedures necessitating high cutting forces that might break or damage the relatively fragile 11 inner member.
12 The structural configuration, limited cutting effectiveness 13 and minimal strength of presently available curved and straight-14 sided cutting teeth typically limit instruments utilizing these cutting teeth to specific cutting functions and types o~ tissue.
16 Such instruments cannot be employed, for example, ts perform 17 multiple, diverse cutting functions, such as resecting, trimming, 18 side cutting, whiskering, burring and the like, on diverse types of 19 tissue including relatively elastic tissue as well a~ relatively hard tissue, such as hone. The functional limitations of such 21 instruments make it necessary to utilize many specialized cutting 22 instruments in surgical procedures, such as arthrosopy, involving 23 multiple, diverse cutting operations on different types of tissue, 24 thereby adding signi~icantly to the time and complexity of these procedu~es.
26 A further drawback shared by surgical cutting instruments of 2~75~
1 the type described is that a gap is usually maintained between the 2 outer sleeve and the inner tube to permit the inner tube to freely 3 rotate within the outer sleeve without friction and thP attendant 4 and potentially damaging heat. This gap, however, is typically wide enough adjacent the cutting teeth for tissue to be drawn 6 therein. Tissue is thusly caught between the outer sleeve and the 7 rotating inner tube and, when the inner tube is rotated at high 8 speeds, the tissue becomes wrapped around the inn~r tube. When 9 this occurs, rotation of the inner tube is impeded and sometimes totally blocked, requiring time and attention to be diverted from 11 the surgical procedure to ~ree the caught tissue. Moreover, the 12 ', gap between the inner and outer tubes tends to promote misalignment 13 between these tubes when cutting forces are imposed between them.
14 Since there is no structure in the gap to preserve positional stability of the inner tube, the resulting misalignment impairs the 16 cutting efficiency and effectiveness of the surgical instrument.
18 Accordingly, it is a primary ob j ect of the present invention 19 to overcome the above-mentioned disadvantages associated with prior art cutting instrument~ having curved or straight-sided cutting 21 teeth~
22 It is another object of the invention to provide a surgical 23 cutting instrument having cutting te~th capable of performing 24 diverse cutting operations on different types of tissu~, including bone.
2 ~
1 A further object of the invention is to provide a surgical 2 cutting instrument having cutting teeth formed in a rotatable tube 3 capable of applying large cutting forces.
4 An additional object of the invention is to provide a surgical cutting instrument having a rotatable inner member carrying cutting 6 teeth capable of cutting relatively large quantities of tissue 7 during each rotation of the inner member.
8 Yet another object of the invention is to provide a surgical 9 cutting instrument of the type described wherein the e~fective cutting length provided by cutting teeth is signi~icantly longer 11 then in prior art instruments.
12 It is also an object of the in~ention to prevent misalignment 13 between the toothed rotating inner member and the outer tubular 14 member in a surgical cutting instrument of the type described.
A still fur~her ob~ect o~ the invention is to prevent tissue 16 from being trapped or jammed between a toothed cutting edge on 17 rotating inner member and a cutting edge on an apertured outer 18 tubular member coaxially receiving the inner member.
19 Among the advantages of the surgical cuttiny instrument of the present invention over the prior art are: reduced time required to 21 surgically cut tissue; increased strength of the cutting tePth 22 resulting from minimizing the quantity of material removed ~rom the 23 inner member in forming teeth edges; minimization of damaging 24 frictional heat from high speed rotation of the inner mamber within the outer member; and elimination of the need for multiple 26 specialized cutting instruments to ef~ect different types of cuts 2~7~
1 in certain surgical procedures, in particular, arthroscopic 2 procedures.
3 These and other objects, benefit~ and advantages are achieved 4 with the surgical cutting instrument of the present invention as S characterized by an o~lter tubular member including a proximal end 6 and a distal end ~lith a cutting aperture for receiving tissue, and 7 a coaxially received inner tubular member including a proximal end 8 and a toothed distal end for cutting tissue. The inner member 9 distal end includes a distal cutting edge segment angularly joined to toothed cutting edge segments disposed symmetrically along 11 opposite sides of the inner member. The distal end of the inner 12 member contacts the inner surface of the outer mPmber distal end at 13 a single bearing contact point on the rotation axis to positionally 14 stabilize and support the inner member and prevent misalignments between the members. Each toothed cutting edge segment includes a 16 plurality of longitudinally aligned cutting teeth extending 17 proximally from the distal cutting edge segment. The cutting teeth 18 are defined by straight sides converging at coplanar crests, and l9 joined by coplanar roots, the plane of the roots being parallel to the plane of the crests but located closer to the longitudinal axis 21 (i.e., the rotation axis) of the inner member. The location of 22 these planes is such that at least 80% of the height of each 23 cutting tooth extends into the semi-cylindrical side oP the inner 24 member from which most of the material has been removed to form the teeth. In addition, the height o~ the teeth is at least 50% of 26 their width and on the order of 15% to 22% of the inner member 1 diameter. Respective concave transition segments join the toothed 2 cutting edge segments to the distal leading cutting edge segment.
3 Respective rearward concave sides of the most proximal teeth serve 4 as transitions to inclined edge segments extending from a centered proximal edge segment. The cutting aperture in the outer member is 6 circumscribed by a cutting edge ~ormed by cuttin~ a section in a 7 plane positioned angularly with the central longitudinal axis of 8 the outer member. A clearance gap between the inner and outer 9 members is interrupted only by the single bearing contact point.
The gap has a predetermined width but tapers to a relatively narrow 11 width between the edge of the cutting aperture and th~ cutting 12 teeth to prPvent tissue from being drawn between the cutting 13 aperture and the teeth and becoming wrapped around th inner 14 member.
Other objects and advantages of the present invention will 16 become apparent from the following description of the preferred 17 embodiments taken in conjunction with the accompanying drawings.
19 Fig. 1 is a broken, exploded side view, partly in section, of the surgical cutting instrument according to the present invention.
21 Fig. 2 is a broken side view, partly in section, of the 22 surgi~al cutting instrument of Fig. 1 with a handpiece drive unit.
23 Fi~. 3 is a broken side view, partly in section, of the distal 24 end of the outer tubular member of the surgical cutting instrument o~ ~ig. 1 ~a7~
1 Fig. 4 is a view in sec~ion of the outer tubular member taken 2 along line 4-4 of Fig. 3.
3 Fig. 5 is a broken side view of the distal end of the inner 4 tubular member of the surgical cutting instrument of FigO 1.
Fig. 6 is a broken, ~op view of the distal end of the inner 6 tubular member of the inner tubular member of the surgical cutting 7 instrument of Fig. 1.
8 Fig. 7 is a broken side YieW of the distal end of an 9 alternative embodiment of an inner tubular member of the surgical cutting instrument according to the present invention.
11 Fig. 8 is a broken side view of the distal end of the surgical 12 cutting instrument according to the present invention showing the 13 inner tubular member being rotated with respect to the outer 14 tubular member.
Fig. 9 is a view in section of the surgical cutting instrument 16 taken along line 9-9 of Fig. 8.
17 Fig. 10 is a view in section of the surgical cutting 18 instrument taken along line 10-10 of Fig. 8.
As shown in Figs~ 1 and 2, a surgical cutting instrument 12 21 according to the present invention includes an elongate outer 22 tubular member 14 and an elongate inner tubular member 16 rotatably 23 disposed within the outer member 1~. The surgical cutting 24 instrument 12 is particularly configured to be received in and driven by a handpiece drive unit 18 having a distal end shown in 20~a~
1 Fig. 2. Handpiece drive unit 18 is the handpiece of the Concept 2 Model 9950 INTRA-ARC Drive System, and reference is made thereto 3 for more specific detail relating to the structure and operation of 4 the handpiece. The handpiece drive unit 18 is described herein only to the extent required ~o understand the operation o~ the 6 surgical cutting instrument 12.
7 Handpiece drive unit 18 includes a yenerally cylindrical body8 20 having an enlarged forward end 22 sealed by a locking ring 24, 9 a longitudinally extending cylindrical bore having a rearward boresection (now shown) for housing a drive motor, an intermediate bore 11 section 26 receiving a drive shaft 28 rotatably driven by the drive 12 motor, a forward bore section 30 receiving the proximal end of the13 surgical cutting instrument 12, and an aspirating chamber 32 14 positioned between the intermediate bore section 26 and the forward bore section 30. The aspirating chamber 32 communicates with a 16 vacuum source (not shown) via suction channels 34 and 36 formed in17 the body 20. A plurality of push-button switches 38 are dispose~
18 on the handpiece drive unit 18 to control operation of the drive 19 motor.
Locking ring 24 includes an exposed forward-~acing surface, a 21 rearward-facing surface abutting the forward end 22 of body 20 and22 an annular lip 40 extending axially over a short len~th of the 23 forward end 22. A circular recess in the forward facing surface is24 disposed concentrically about a central aperture 42, and two arcuat~ channels are defin~d through the locking ring within the 26 recess ~qually spaced from a slot therein and dispos~d 2 ~
1 symmetrically about aperture 42. Each channel subtends 2 approximately 90 of arc at a constant radial distance from the 3 center of aperture 42. A disc-shaped spacer 44 is disposed in ~he 4 locking ring recess and has a central aperture aligned with the aperture 42. Spacer 4~ is secured via screws to body 20, the 6 screws passing ~hrough the two respective arcuate channels to 7 permit the locking ring 24 to be rotated relative to the spacer 44 8 and the body 20, limited by the arcuate lengths o~ the channels 9 (i.e., 90~). Spacer 44 also has a slot extending axially therethrough to a prescribed radial depth from the central 11 aperture, such that when the spac~r slok is rotatably aligned with 12 ~- the slot in the locking ring 24 and with a slot 46 in the forward 13 bore section 30, a locator stub 48 on the proximal end of the 14 surgical cutting instrument 12 can freely pass into and out of the handpiece drive unit 18.
16 The rearward-facing surface of the locking ring 24 includes an 17 arcuate ramp surface extending approximately 140~ from the slot 18 along the outer edge of the aperture ~2 to serve as a camming 19 surface for inserting the proximal end of the surgical cutting instrument 12 int~ the handpiece drive unit 18. In one extreme 21 rotational position of the locking ring 24, the slot in the locking 22 ring 24 is aligned with the slot in the spacer ~4 and with the slot 23 46 in the forward bore section 30, whereby the surgical cutting 24 instrument 12 can be inserted through the locking ring 24 sufficiantly far that an open end thereof slides over the forward 26 end of the drive shaft ~8, and the locator stuh 48 is disposed in ri ~
1 slot 46 with just a small portion of the stub projecting partially 2 into the locking ring slot. If the locking ring 24 is then rotated 3 90 to its other extreme position, the camming surface gradually 4 forces the locator stub 48, and with it the surgical cutting instrument 12, rearwardly to produce positive engagement with the 6 drive shaft 28. The two extreme positions of the locking ring 24 7 are maintained by a detent ball 50 and a spring 52 located in a 8 recess in the forward end 2~ of the body 20. The detent ball and 9 spring 52 cooperate with two dimples formed at 90 spaced locations 10 in the rearward-facing surface of the locking ring 24 to provide 11 stops at the two extreme rotational positions o~ the locking ring.
12 In order to remove the surgical cutting instrument 12 from the 13 handpiece drive unit 18, the locking ring 24 is rotated 90' in the 14 opposite direction to its initial extreme position. When the slot 15 in the locking ring 24 becomes aligned with the spacer slot 44 and 16 the slot 46, the surgical cutting instrument 12 can be easily 17 removed from the handpiece drive unit.
18 A hub 54 is mounted on a proximal end 56 of the outer tubular 1~ member 14, the hub 54 being made o~ plastic or metal and havlng a 20 generally cylindrical configuration with the locator stub 48 21 extending radially therefrom to be received in the slots in the 22 handpiece drive unit 18 as described above. Hub 54 includes a 23 cylindrical recess 58 defined in its proximal end in communication 24 with a distally extending central bore 60 for receiving the 25 proximal end 56 of the outer member 14. A spring 62 is disposed in 26 recess 58 and includes four equally spaced arms extending radially 2 ~
1 from a central aperture 64 along the bottom of recess 58 and bent 2 to extend proximally along the cylindrical side wall of th~ recess.
3 One pair 66 of opposing spring arms has curved inwardly bent ends 4 to engage the inner member 14, while the other pair of opposing spring arms 68 has square outwardly bent ends to hold the spring 62 6 in place in the recess 58.
7 A hub 70 is secured to the proximal end 72 of the inner 8 tubular member 16 and has a bevelled front lip 74 received in 9 recess 58 in hub 54 of outer member 14 so as to be held in place by spring arms 66. The proximal end 72 of inter tubular member 16 is 11 secured in and extends through an axial bore in hub 70 to 12 communicate with a passage 76 extending diametrically through hub 13 70 to be disposed in the aspirating chamber 32 in handpiece drive 14 unit 18. A pair of radial ribs 78 is positioned rearwardly of the passage 76 and extend longitudinally to a chamfered lip 80 carrying 16 a rearwardly projecting driven tang 82 adapted to be received in 17 drive shaft 28. A sleeve 84 is telescopically mounted over ribs 78 18 and drive tang 82, and is spring biased away from lip 80. ~s 19 illustrated in Fig. 2, wherein sleeve 84 is not shown, inner member 16 is rotatably driven within the outer member 14 by drive shaft 28 21 engaging the driven tang 82, while suction is produced in the inner 22 member 16 via the channels 34 and 36 communicating with the vacuum 23 source and passage 76. Although the surgical cutting instrument of 24 the present invention is shown and described for use in the Concept 2S INTRA-ARC system, it will be appreciated that the surgical cutting 26 instrument of the present invention can have any de~ired hub 1 configuration to be utilized with any drive system or handpiece 2 capable of rotating an elongate inner tubular member within an 3 elongate outer tubular member to cut or otherwise engage bodily 4 tissue at the distal end.
The outer tubular member ~4 is preferably made of a length of 6 stainless steel tubing having the proximal end 56 adhesively 7 secured in bore 60 of hub 54, and a distal end 86 configured as a 8 segment of a hemisphere and having an aperture or opening 88 9 defined therein to form a cutting port or window. As shown in Figs. 3 and 4, orifice 88 is formed by taking a section through a 11 plane inclined at an angle of approximately 15 to the longitudinal 12 ~ axis Y of outer member 14 and intersecting that axis slightly 13 forward of distal end 86 of that member. Orifice 88 is thus 14 circumscribed by a flat edge 90 of generaily elliptical configuration. The width of edge 90 in determined by the thickn~ss 16 of tubular member 14 in the inclined section plane. Edge 90 17 thereby defines a sharp cutting edge corner 98 at its intersection 18 with the inner surface of outer member i4. The cutting edge corner 19 98 is thus contained in a plane disposed at the acut~ section angle with central longitudinal axis Y of outer tubular member 14.
21 The inner tubular member 16 is preferably formed of length of 22 stainless steel cylindrical tubing having its proximal end 72 23 adhesively secured in hub 70. The distal end 100 of member 16 is 24 in the ~orm of a segment of a hemisphere and includes a cutting edge 102 rotatable past cutting edge corner 98 on outer member 14 26 to engage and cut tissue positioned in aperture 88 when inner 1 member 16 is rotatably driven within the outer member 14 by drive 2 shaft 28~ ~s shown in Figs. 5 and 6, cutting edge 102 is formed by 3 cutting away part of the distal end of member 16 and includes a 4 distal segment 104 arcuately configured and joined at its ends to side segments 106 extending longitudinally along respective 6 opposite sides of the inner member 16. Distal edge segment 104 is 7 an exposed arcuate edge of distal end 100 and is displaced 8 laterally from the central longitudinal axis X of member 16 (i.e., 9 slightly above that axis as viewed in Fig. 5). The opposite ends of distal edge segment 104 are co-planar and taper and a proximal 11 direction toward axis X at an angle of approximately 15. Side 12 - edge segments 106 ext~nd from respective ends of distal edge 13 segment 104 and are each formed as a series of longitudinally 14 aligned cutting teeth including distal tooth 116, proximal tooth 118 and intermediate teeth 114, all of generally triangular 16 configuration. Each tooth 114, 116, 118 is laterally aligned with 17 a corresponding tooth on the opposite side edge segment 106. A
18 smooth concave transition 112 between the tapering distal edge 19 segment 104 and the most distal tooth 116 in each series has a radius of curvature significantly smaller than the height (i.e., 21 along the tube circumference) and width (i.e.l along the tube 22 length) of the adjacent most distal tooth 116. Each cutting tooth 23 114, 116, 118 is defined by straight forward and rearward sides 120 24 and 122, respectively, converging symmetrically at an angle A to a crest 124. All of crests 124 are disposed in a first common plane.
26 The forward and rearward sides of adjacent teeth similarly 1 intersect at respective roots 126 located in a second common plane.
2 The crest plane and root plane are parallel to one another and to 3 the axis X of inner member 16. The plane of roots 126 is disposed 4 closer to axis X than is the plane of crests 124 whereby at least 80% (and preferably 90% or more) o~ the height of the teeth are 6 disposed on the same hemispherical side of axis X from which 7 material has been cut away to form the teeth. With this 8 configuration the tubular inner member 16 is circumferentially 9 continuous at said crests over an arc in excess o~ 180. In addition, the height of the teeth is no less than 50~ of their 11 width between roots 126 and, preferably, is between 60% and 70% of 12 ; the width. The rearward side 128 of the most proximal tooth 118 is 13 arcuate and defined by a radius of curvature considerably larger 14 than the radius of curvature of distal transition segment 112.
Rearward side 128 merges smoothly into a straight forward-facing 16 edge segment 130 inclined at substantially the same angle from axis 17 X as the forward sides 120 of teeth 114. Segment 130 extends to a 18 proximal edge segment 132 joining the two side segments 106 and 19 disposed on the same side of axis X as distal segment 104.
As best illustrated, in Fig. 10, an annular clearance gap 134 21 is provided between the outer surface of the inner member 16 and 22 the inner surface of the outer member 14 to permit high speed 23 rotation of the inner member within the outer member without 24 frictional engagement and the resulting heat that might damage the cutting instrument 12. Gap 134 extends substantially the entire 26 length of outer and inner members 14 and 16; however, the gap 2~75~
1 clearance tapers to reduced width sections 136 extending 2 longitudinally along both side segments 106 of cutting edge 102 3 (i.e., in the region of the teeth 114, 116 and 118). The gap 4 clearance 134 also tapers to a contact point 138 at the facing distal ends of the outer and inner tubular members 14 and 16.
6 Specifically, the inner surface of the distal end of outer tubular 7 member 14 contacts the outer surface of distal end 100 of inner 8 tubular member 16, and the bearing contact point 138 resides on the 9 coaxially disposed central longitudinal axes X and Y (i.e., the axis of rotation).
11 Preferably, angle A formed by the sides of cutting tPeth 114, 12 '116 and 118, is in the range of 66' to 77; the height of the 13 cutting teeth 114, 116 and 118 measured as the distance between the 14 plane of crests 124 and the plane of roots 126, is in the range of 15% to ~2% of the outer diameter of inner member 16; edge segments 16 130 define an angle of 50 to 60 with respect to the central 17 longitudinal axis X of inner member 16; ~he longitudinal plane 18 containing rooks 126 is at or close to axis X, whereas the plane 19 containing the crests 124 is more remote from that axis, so that between 90% and 100% height of teeth 114, llS, 118 r~side on the 21 ~emi-cylindrical side of the axis toward which the teeth generally 22 point: the plane containing edge 90 and edge corner 98 on the outer 23 member 14 defines an angle of approximately 15 with respect to the 24 central longitudinal axis Y of the outer member; and the width of gap 134 is approximately .0005 inches and the width of th~ narrowed 26 width sections 136 is approximately .00025 inches.
2 ~
1 Although the side cutting edge segments 106 are depicted in 2 Fig. 5 as including five cutting teeth on each side, the exact 3 number of teeth can vary in accordance with the diameter of inner 4 member 16, there being fewer cutting teeth provided on smaller diameter inner members. As shown in Fig~ 7, a relatively small 6 diameter inner tubular member 216 includes four cutting teeth 214 7 on each side segment 206.
8 The relative proportions and configurations describPd herein 9 produce numerous advantages. The straight configuration for the forward and rearward facing tooth sides 120 and 122 strengthens the 11 cutting teeth 114, 116, 118 by minimizing the quantity of metal 12 material that must be removed from inner member 16 to form the 13 teeth. In addition, the straight tooth sides effect a shearing 14 action as opposed to tearing the tissue. The straight forward and rearward facing tooth sides are effective in cutting tissue, 16 including bone, for the entire height of the cutting teeth, and the 17 crest angle A provides effective shear cutting in both relatively 18 soft and hard tissue. The specified range of heights of the 19 cutting teeth relative to the outer diameter of the inner tubular member 16, and the range of tooth heights relative to tooth widths, 21 provides structurally strong cutting teeth. The strong cutting 22 teeth minimize tooth breakage and enable the teeth to shear large 23 quantities of tissue during each passage of a cutting edge side 24 region 106 past the aperture 88. The location of the plane containing roots 126 proximate the central longitudinal axis X of 26 the inner member 16 further increases the strength of the cutting 2 ~ ~ ~3 ri ~ ~3 1 end of member 16 by providing a larger structural support than i5 2 present when little or no part of the teeth project into the 3 semicylindrical region opposite the support structure for the 4 teeth. The angular orientations of the distal edge segment 104, concave transitions 112, arcuate segments 12~ and the forward-~ facing segments 130 are selected to further minimize the quantity 7 o~ metal material removed from the inner member 16 during machining 8 and, thereby, enhance the structural integrity of thak member. The 9 angular orientation of edge 90 and its corner 98 relative to axis Y of outer member 14 reduces the amount of material removed from 11 the outer member and thusly ~trengthens that member while providing 12 controlled, sequential cutting of tissue when one of the side edge 13 segments 106 is rotated past the cutting edge corner 98. The 14 distal contact point 138 supports and positionally stabilizes the inner tubular member 16 as it rotates in outer tubular member 14 to 16 prevent misalignment of the members at high rotation speeds.
17 Contact point 138 serves to further positionally stabiliæe the 18 inner member 16 when large cutting forces are imposed and, 19 therefore, permits hard tis~ue, such as bone, to be cut without deforming member 16. The reduced width sections 136 of the 21 clearance gap 134 prevent tissue from being drawn between the 22 members and becoming wrapped around the rotating inner member 16.
23 In operation, the surgical cuttinq instrument 12 is inserted 24 into handpiece drive unit 1~ in the manner described above and is positioned at the surgical site through a portal for arthroscopic 26 surgery. The speed and operation of the surgical cutting lg 2~7~
1 instrument 12 is controlled by switches 38, and the surgeon 2 advances the surgical cutting instrument 12 to position tissue, 3 such as bone and meniscus cartilage, within aperture 88 in outer 4 tubular member 14. As shown in Fig. 8, the inner member 16 is rotatably driven within the outer member 14, such that a portion of 6 the distal cutting edge segment 104 and one of the cutting edge 7 side segments sequ~ntially penetrate and cut tissue when rotated 8 past the cutting edge cornex 98. Severed tissue is aspirated 9 through the lumen of the inner tubular member 16 to exit the surgical instrument 12 via the passage 76 communicating with the 11 aspirating chamber 32 in the handpiece drive unit 18. The cutting 12 teeth 114, 116, 118 produce an aggressive cutting action in tissue, 13 including bone, and the converging forward and rearward facing 14 tooth sides 120 and 122 cut tissue in a shearing action rather than a tearing or digging type of cut. As shown in Fig. 9, the crPsts 16 126 of the straight-sided, triangular shaped teeth pierc and grip 17 tissue 140 positioned in the outer member aperture 88, and pull the 18 tissue into such opening as the inner member 16 rotates. The 19 forward and rearward facing sides 120 and 122 of the teeth continue to cut through the tissue 140 in a shearing action as the teeth 21 move across the opening 88. The surgical cuttiny instrument 12 22 possesses the ability to perform diverse cutting operations on both 23 so~t and hard tissue that would normally necessitate the use of 24 diverse, specialized ~utting blades. For example, the surgical cutting instrument 12 can be utilized as a ~ull radius resector, a 26 synovial r~sector, a trimmer, a meniscus cutter, a side cutter, a .5 ~
1 whisker, an arthroplasty burr, and the like, for cutting, shaping 2 and finishing bone surfaces as well as other types of tissue.
3 Having de~scribed a preferred e~bodiment of a new and improved 4 surgical cutting instrument constructed in accordance with the present invention, it is believed that other modifications, 6 variations and changes will be suggested to those skilled in the 7 art in view of the teachings set forth herein. It is therefore to 8 be understood that all such variations, modifications and changes 9 are believed to fall within the scope of the present invention as defined by the appended claims.
Claims (28)
1. A surgical cutting instrument for cutting tissue comprising an elongate outer tubular member having a proximal end, a distal end and a longitudinal axis;
cutting port means at said distal end for receiving tissue;
an elongate inner tubular member having a proximal end and a distal end;
tissue cutting means on said inner member distal end including a plurality of straight-sided triangular cutting teeth;
and mounting means for securing said inner member coaxially within said outer member to permit selective rotation of said inner member relative to said outer member, wherein the distal end of said inner member is in engagement with the distal end of said outer member, and wherein said cutting means is positioned to cut tissue received through said cutting port means when said inner member is rotated in said outer member.
cutting port means at said distal end for receiving tissue;
an elongate inner tubular member having a proximal end and a distal end;
tissue cutting means on said inner member distal end including a plurality of straight-sided triangular cutting teeth;
and mounting means for securing said inner member coaxially within said outer member to permit selective rotation of said inner member relative to said outer member, wherein the distal end of said inner member is in engagement with the distal end of said outer member, and wherein said cutting means is positioned to cut tissue received through said cutting port means when said inner member is rotated in said outer member.
2. A surgical cutting instrument as recited in claim 1 wherein the distal end of said outer member includes an end wall having an outer surface and an arcuate inner surface:
wherein the distal end of said inner member is an end wall having an arcuate outer surface; and wherein said engagement of said distal ends comprises a bearing contact, on said longitudinal axis, between said arcuate inner surface and said arcuate outer surface.
wherein the distal end of said inner member is an end wall having an arcuate outer surface; and wherein said engagement of said distal ends comprises a bearing contact, on said longitudinal axis, between said arcuate inner surface and said arcuate outer surface.
3. A surgical cutting instrument as recited in claim 4 wherein said bearing contact is the only contact between said inner and outer members distally of the proximal end of said outer members.
4. A surgical cutting instrument as recited in claim 2 further including a clearance gap between said inner and outer members totally surrounding said bearing contact.
5. A surgical cutting instrument as recited in claim 4 wherein said clearance gap has a predetermined width throughout except for a relatively narrow width proximate said tissue cutting means to prevent severed tissue from being drawn into said gap.
6. A surgical cutting instrument as recited in claim 5 wherein said narrow width is approximately one-half said predetermined width.
7. A surgical cutting instrument as recited in claim 6 wherein said predetermined width is approximately .0005 inches and said narrow width is approximately .00025 inches.
8. A surgical cutting instrument for cutting tissue comprising a elongate outer tubular member having a proximal end, a distal end and an outer cutting edge at said distal end;
an elongate inner tubular member having a central longitudinal axis, a proximal end, a distal end and an inner cutting edge at said distal end, said inner cutting edge defining a plurality of triangular cutting teeth each having straight linear sides converging to a crest, said inner member being coaxially and rotatably received in said outer member to position said inner cutting edge adjacent said outer cutting edge and to permit said inner cutting edge to move past said outer cutting edge to cut tissue; and a clearance gap disposed between said inner and outer members, said gap having a predetermined width tapering to a relatively narrow width between said outer cutting edge and said inner cutting edge.
an elongate inner tubular member having a central longitudinal axis, a proximal end, a distal end and an inner cutting edge at said distal end, said inner cutting edge defining a plurality of triangular cutting teeth each having straight linear sides converging to a crest, said inner member being coaxially and rotatably received in said outer member to position said inner cutting edge adjacent said outer cutting edge and to permit said inner cutting edge to move past said outer cutting edge to cut tissue; and a clearance gap disposed between said inner and outer members, said gap having a predetermined width tapering to a relatively narrow width between said outer cutting edge and said inner cutting edge.
9. A surgical cutting instrument as recited in claim 8 wherein said clearance gap extends longitudinally between said inner member and said outer member from said distal ends to said proximal ends.
10. A surgical cutting instrument as recited in claim 9 wherein said outer cutting edge extends longitudinally on said outer member and said inner cutting edge extends longitudinally on said inner member.
11. A surgical cutting instrument as recited in claim 10 wherein said narrow width is approximately one-half said predetermined width.
12. A surgical cutting instrument as recited in claim 11 wherein said predetermined width is approximately .0005 inches and said narrow width is approximately .00025 inches.
13. A surgical cutting instrument as recited in claim 10 wherein said crests are disposed in a first common plane extending longitudinally of said inner member, wherein said teeth are separated by a series of roots disposed in a second common plane oriented parallel to said first plane and closer than said first plane to said longitudinal axis.
14. A surgical cutting instrument as recited in claim 13 wherein said inner member has a predetermined outer diameter, and wherein the height of said teeth measured between said first and second planes is at least 15% of said outer diameter.
15. A surgical cutting instrument as recited in claim 13 wherein the height of said teeth measured between said first and second planes is in the range of 60% to 70% of the width of said teeth measured between said roots.
16. A surgical cutting instrument for cutting tissue comprising an elongate outer tubular member having a proximal end, a distal end and a longitudinal axis;
an opening at said distal end circumscribed by a planar edge disposed angularly with said axis;
an elongate inner tubular member rotatably received in said outer member and having a proximal end, a distal end and a longitudinal axis; and tissue cutting means at said inner member distal end including an arcuate leading cutting edge segment angularly disposed with respect to said inner member longitudinal axis, and first and second toothed cutting edge segments joined to respective opposite ends of said leading cutting edge segment, said toothed cutting edge segments being symmetrically disposed about said longitudinal axis and including a plurality of cutting teeth each having straight sides converging to a crest, wherein said inner member at corresponding crests of said first and second toothed cutting edge segments is circumferentially continuous over an arc in excess of 180°, said cutting means being positionable adjacent said opening to cut tissue through said opening when said inner member is rotated in said outer member.
an opening at said distal end circumscribed by a planar edge disposed angularly with said axis;
an elongate inner tubular member rotatably received in said outer member and having a proximal end, a distal end and a longitudinal axis; and tissue cutting means at said inner member distal end including an arcuate leading cutting edge segment angularly disposed with respect to said inner member longitudinal axis, and first and second toothed cutting edge segments joined to respective opposite ends of said leading cutting edge segment, said toothed cutting edge segments being symmetrically disposed about said longitudinal axis and including a plurality of cutting teeth each having straight sides converging to a crest, wherein said inner member at corresponding crests of said first and second toothed cutting edge segments is circumferentially continuous over an arc in excess of 180°, said cutting means being positionable adjacent said opening to cut tissue through said opening when said inner member is rotated in said outer member.
17. A surgical cutting instrument as recited in claim 16 wherein said cutting teeth in each toothed cutting segment are linearly aligned on said inner member in a series of teeth extending longitudinally from said leading cutting edge segment toward the proximal end of said inner member.
18. A surgical cutting instrument as recited in claim 17 wherein said cutting teeth are joined by roots disposed in a first longitudinally extending plane disposed proximate said inner member longitudinal axis, and wherein the crests of said cutting teeth are disposed in a plane oriented parallel to the plane containing said roots but more remote from the longitudinal axis of said inner member.
19. A surgical cutting instrument as recited in claim 18 wherein said toothed cutting edge segments each include a most proximal cutting tooth joined to respective ends of a proximal arcuate cutting edge segment.
20. A surgical cutting instrument as recited in claim 19 wherein said proximal arcuate cutting edge segment is disposed on the same side of the inner member longitudinal axis as the plane containing said crests.
21. A surgical cutting instrument as recited in claim 20 wherein said inner member includes a generally forward-facing cutting edge segment disposed angularly with respect to said inner member longitudinal axis, and wherein said proximal arcuate cutting edge segment is joined to said forward-facing cutting edge segment.
22. A surgical cutting instrument a recited in claim 21 wherein said leading cutting edge segment is joined to said toothed cutting edge segment by a distal curved edge segment.
23. A surgical cutting instrument as recited in claim 22 wherein said leading cutting surface converges distally at an acute angle toward said inner member longitudinal axis.
24. A surgical cutting instrument as recited in claim 18 wherein said converging surfaces define an angle at said crests of approximately 66' to 77°.
25. A surgical cutting instrument as recited in claim 18 wherein the distance between said first and second planes is approximately 15% to 22% of the outer diameter of said inner member.
26. A surgical cutting instrument as recited in claim 18 wherein the distance between said first and second planes is at least 50% of the spacing between successive roots.
27. A surgical cutting instrument as recited in claim 18 wherein said forward-facing cutting edge segment is disposed at an angle of approximately 50° to 60° with said inner member longitudinal axis.
28. A surgical cutting instrument as recited in claim 27 wherein the planar edge circumscribing said opening is contained in a plane disposed at an angle of approximately 14° to 16° with said outer member longitudinal axis.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US07/655,035 | 1991-02-14 | ||
| US07/655,035 US5217479A (en) | 1991-02-14 | 1991-02-14 | Surgical cutting instrument |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA2060758A1 true CA2060758A1 (en) | 1992-08-15 |
Family
ID=24627217
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002060758A Abandoned CA2060758A1 (en) | 1991-02-14 | 1992-02-06 | Surgical cutting instrument |
Country Status (5)
| Country | Link |
|---|---|
| US (1) | US5217479A (en) |
| EP (1) | EP0499465A1 (en) |
| JP (1) | JPH0595963A (en) |
| AU (1) | AU644265B2 (en) |
| CA (1) | CA2060758A1 (en) |
Families Citing this family (141)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6120502A (en) | 1988-06-13 | 2000-09-19 | Michelson; Gary Karlin | Apparatus and method for the delivery of electrical current for interbody spinal arthrodesis |
| US6923810B1 (en) | 1988-06-13 | 2005-08-02 | Gary Karlin Michelson | Frusto-conical interbody spinal fusion implants |
| US7534254B1 (en) | 1988-06-13 | 2009-05-19 | Warsaw Orthopedic, Inc. | Threaded frusto-conical interbody spinal fusion implants |
| CN1128944A (en) | 1988-06-13 | 1996-08-14 | 卡林技术公司 | Apparatus and method of inserting spinal implants |
| US7491205B1 (en) | 1988-06-13 | 2009-02-17 | Warsaw Orthopedic, Inc. | Instrumentation for the surgical correction of human thoracic and lumbar spinal disease from the lateral aspect of the spine |
| US6770074B2 (en) | 1988-06-13 | 2004-08-03 | Gary Karlin Michelson | Apparatus for use in inserting spinal implants |
| US5454378A (en) * | 1993-02-11 | 1995-10-03 | Symbiosis Corporation | Biopsy forceps having a detachable proximal handle and distal jaws |
| US5269797A (en) * | 1991-09-12 | 1993-12-14 | Meditron Devices, Inc. | Cervical discectomy instruments |
| US5833692A (en) * | 1993-01-29 | 1998-11-10 | Smith & Nephew, Inc. | Surgical instrument |
| DE69409565T2 (en) * | 1993-01-29 | 1998-10-01 | Smith & Nephew Inc | Swiveling curved instrument |
| US5620447A (en) * | 1993-01-29 | 1997-04-15 | Smith & Nephew Dyonics Inc. | Surgical instrument |
| DK0703757T3 (en) | 1993-06-10 | 2003-12-29 | Karlin Technology Inc | Spinal implant insertion device |
| US5489291A (en) * | 1994-02-23 | 1996-02-06 | Wiley; Roy C. | Apparatus for removing tissue during surgical procedures |
| US5649547A (en) | 1994-03-24 | 1997-07-22 | Biopsys Medical, Inc. | Methods and devices for automated biopsy and collection of soft tissue |
| US5526822A (en) * | 1994-03-24 | 1996-06-18 | Biopsys Medical, Inc. | Method and apparatus for automated biopsy and collection of soft tissue |
| US5507795A (en) * | 1994-04-29 | 1996-04-16 | Devices For Vascular Intervention, Inc. | Catheter with perfusion system |
| US5531756A (en) * | 1994-08-02 | 1996-07-02 | Larose; Daniel J. | Arthroscopic surgical punch |
| US5569284A (en) * | 1994-09-23 | 1996-10-29 | United States Surgical Corporation | Morcellator |
| US5562694A (en) * | 1994-10-11 | 1996-10-08 | Lasersurge, Inc. | Morcellator |
| US5601583A (en) * | 1995-02-15 | 1997-02-11 | Smith & Nephew Endoscopy Inc. | Surgical instrument |
| US6758849B1 (en) | 1995-02-17 | 2004-07-06 | Sdgi Holdings, Inc. | Interbody spinal fusion implants |
| CA2214272A1 (en) * | 1995-03-02 | 1996-09-06 | Benny Gaber | Uterine tissue collector |
| US5618293A (en) * | 1995-06-06 | 1997-04-08 | Smith & Nephews Dyonics, Inc. | Surgical instrument |
| US5676012A (en) * | 1995-12-05 | 1997-10-14 | Spectrum Manufacturing, Inc. | Process for forming endoscopic shaver blade from elongate tube |
| US5863294A (en) * | 1996-01-26 | 1999-01-26 | Femrx, Inc. | Folded-end surgical tubular cutter and method for fabrication |
| US5709698A (en) * | 1996-02-26 | 1998-01-20 | Linvatec Corporation | Irrigating/aspirating shaver blade assembly |
| US5823970A (en) * | 1996-03-22 | 1998-10-20 | Medical Device Technologies, Inc. | Biopsy needle set |
| US5817032A (en) | 1996-05-14 | 1998-10-06 | Biopath Automation Llc. | Means and method for harvesting and handling tissue samples for biopsy analysis |
| US6342061B1 (en) | 1996-09-13 | 2002-01-29 | Barry J. Kauker | Surgical tool with integrated channel for irrigation |
| US5792167A (en) * | 1996-09-13 | 1998-08-11 | Stryker Corporation | Surgical irrigation pump and tool system |
| US5730752A (en) * | 1996-10-29 | 1998-03-24 | Femrx, Inc. | Tubular surgical cutters having aspiration flow control ports |
| US5741287A (en) * | 1996-11-01 | 1998-04-21 | Femrx, Inc. | Surgical tubular cutter having a tapering cutting chamber |
| US5947990A (en) * | 1997-02-24 | 1999-09-07 | Smith & Nephew, Inc. | Endoscopic surgical instrument |
| US6017316A (en) * | 1997-06-18 | 2000-01-25 | Biopsys Medical | Vacuum control system and method for automated biopsy device |
| WO1999012476A2 (en) | 1997-09-10 | 1999-03-18 | Benny Gaber | Tissue collector |
| US6142955A (en) | 1997-09-19 | 2000-11-07 | United States Surgical Corporation | Biopsy apparatus and method |
| US6053923A (en) * | 1998-03-17 | 2000-04-25 | Arthrotek, Inc. | Method and apparatus for abrading tissue |
| IL124361A0 (en) | 1998-05-07 | 1998-12-06 | Benny Gaber | Uterine tissue collector |
| US5964716A (en) * | 1998-05-14 | 1999-10-12 | Ethicon Endo-Surgery, Inc. | Method of use for a multi-port biopsy instrument |
| US5944673A (en) * | 1998-05-14 | 1999-08-31 | Ethicon Endo-Surgery, Inc. | Biopsy instrument with multi-port needle |
| US6068641A (en) * | 1998-08-25 | 2000-05-30 | Linvatec Corporation | Irrigated burr |
| US7517348B2 (en) * | 1998-09-03 | 2009-04-14 | Rubicor Medical, Inc. | Devices and methods for performing procedures on a breast |
| US6440147B1 (en) * | 1998-09-03 | 2002-08-27 | Rubicor Medical, Inc. | Excisional biopsy devices and methods |
| US6936014B2 (en) * | 2002-10-16 | 2005-08-30 | Rubicor Medical, Inc. | Devices and methods for performing procedures on a breast |
| US6022362A (en) | 1998-09-03 | 2000-02-08 | Rubicor Medical, Inc. | Excisional biopsy devices and methods |
| US7329253B2 (en) * | 2003-12-09 | 2008-02-12 | Rubicor Medical, Inc. | Suction sleeve and interventional devices having such a suction sleeve |
| US6620180B1 (en) | 1998-09-09 | 2003-09-16 | Medtronic Xomed, Inc. | Powered laryngeal cutting blade |
| US20070166834A1 (en) * | 1998-10-05 | 2007-07-19 | Biopath Automation, L.L.C. | Apparatus and method for harvesting and handling tissue samples for biopsy analysis |
| DE29901723U1 (en) | 1999-02-02 | 2000-06-29 | Synthes Ag | Device for extracting bone chips |
| JP4632546B2 (en) | 1999-02-03 | 2011-02-16 | ジンテーズ ゲゼルシャフト ミト ベシュレンクテル ハフツング | Surgical reamer |
| US6742236B1 (en) * | 1999-09-20 | 2004-06-01 | Smith & Nephew, Inc. | Making closed end tubes for surgical instruments |
| US6428539B1 (en) * | 2000-03-09 | 2002-08-06 | Origin Medsystems, Inc. | Apparatus and method for minimally invasive surgery using rotational cutting tool |
| US6712773B1 (en) | 2000-09-11 | 2004-03-30 | Tyco Healthcare Group Lp | Biopsy system |
| US6602203B2 (en) * | 2000-10-13 | 2003-08-05 | Ethicon Endo-Surgery, Inc. | Remote thumbwheel for a surgical biopsy device |
| US20020072739A1 (en) | 2000-12-07 | 2002-06-13 | Roberta Lee | Methods and devices for radiofrequency electrosurgery |
| US6743228B2 (en) | 2001-09-12 | 2004-06-01 | Manoa Medical, Inc. | Devices and methods for tissue severing and removal |
| US20030055315A1 (en) * | 2001-09-14 | 2003-03-20 | Gatto Dominick L. | Method and apparatus for endoscope system |
| US6783533B2 (en) | 2001-11-21 | 2004-08-31 | Sythes Ag Chur | Attachable/detachable reaming head for surgical reamer |
| US20070219459A1 (en) * | 2005-10-14 | 2007-09-20 | Microfabrica Inc. | Biopsy Devices, Methods for Using, and Methods for Making |
| US20030125639A1 (en) * | 2002-01-02 | 2003-07-03 | Fisher John S. | Biopsy needle having rotating core for shearing tissue |
| US7261728B2 (en) * | 2002-03-15 | 2007-08-28 | Ethicon Endo-Surgery, Inc. | Biopsy forceps device and method |
| US7044956B2 (en) * | 2002-07-03 | 2006-05-16 | Rubicor Medical, Inc. | Methods and devices for cutting and collecting soft tissue |
| US20040006355A1 (en) * | 2002-07-03 | 2004-01-08 | Rubicor Medical, Inc. | Methods and devices for cutting and collecting soft tissue |
| US6958071B2 (en) * | 2002-07-13 | 2005-10-25 | Stryker Corporation | Surgical tool system |
| US7179424B2 (en) | 2002-09-26 | 2007-02-20 | Biopath Automation, L.L.C. | Cassette for handling and holding tissue samples during processing, embedding and microtome procedures, and methods therefor |
| EP1545775B1 (en) * | 2002-09-26 | 2010-06-16 | BioPath Automation, L.L.C. | Cassette and embedding assembly, staging devices, and methods for handling tissue samples |
| EP1552266B1 (en) * | 2002-09-26 | 2015-10-28 | BioPath Automation, L.L.C. | Apparatus and methods for automated handling and embedding of tissue samples |
| US7029451B2 (en) * | 2002-11-06 | 2006-04-18 | Rubicor Medical, Inc. | Excisional devices having selective cutting and atraumatic configurations and methods of using same |
| US20070055282A1 (en) * | 2003-03-31 | 2007-03-08 | The Cleveland Clinic Foundation | Apparatus and method for harvesting bone marrow |
| WO2004090111A2 (en) * | 2003-03-31 | 2004-10-21 | The Cleveland Clinic Foundation | Apparatus and method for harvesting bone marrow |
| US7122011B2 (en) * | 2003-06-18 | 2006-10-17 | Rubicor Medical, Inc. | Methods and devices for cutting and collecting soft tissue |
| US9638770B2 (en) | 2004-05-21 | 2017-05-02 | Devicor Medical Products, Inc. | MRI biopsy apparatus incorporating an imageable penetrating portion |
| US7708751B2 (en) | 2004-05-21 | 2010-05-04 | Ethicon Endo-Surgery, Inc. | MRI biopsy device |
| US8932233B2 (en) | 2004-05-21 | 2015-01-13 | Devicor Medical Products, Inc. | MRI biopsy device |
| CH700185B1 (en) * | 2004-07-22 | 2010-07-15 | Orlando Da Rold | Surgical cutting instrument. |
| US7226460B2 (en) * | 2004-08-02 | 2007-06-05 | Karl Storz Endovision, Inc. | Surgical instrument attachment system |
| US20060212060A1 (en) * | 2005-02-11 | 2006-09-21 | Arthrex, Inc. | Arthroscopic shaver and method of manufacturing same |
| US20060196038A1 (en) * | 2005-03-02 | 2006-09-07 | Van Wyk Robert A | Arthroscopic shaver with two pass inner blade and method of manufacturing same |
| US9504521B2 (en) * | 2005-03-17 | 2016-11-29 | Stryker Corporation | Surgical tool arrangement |
| US8123750B2 (en) * | 2005-08-17 | 2012-02-28 | Corespine Technologies, Llc | Apparatus and methods for removal of intervertebral disc tissues |
| US20070116612A1 (en) * | 2005-11-02 | 2007-05-24 | Biopath Automation, L.L.C. | Prefix tissue cassette |
| US8394033B2 (en) * | 2006-07-12 | 2013-03-12 | Boston Scientific Scimed, Inc. | Biopsy device |
| US8177803B2 (en) | 2006-07-19 | 2012-05-15 | Target Medical Innovations, LLC | Endoscopic cutting instruments having improved cutting efficiency and reduced manufacturing costs |
| US7666200B2 (en) * | 2006-07-19 | 2010-02-23 | Target Medical Innovations Llc | Endoscopic cutting instrument with axial and rotary motion |
| CA2665687C (en) | 2006-12-12 | 2016-07-05 | Biopath Automation, L.L.C. | Biopsy support with sectionable resilient cellular material |
| US7938786B2 (en) * | 2006-12-13 | 2011-05-10 | Devicor Medical Products, Inc. | Vacuum timing algorithm for biopsy device |
| US8251916B2 (en) * | 2006-12-13 | 2012-08-28 | Devicor Medical Products, Inc. | Revolving tissue sample holder for biopsy device |
| US20130324882A1 (en) | 2012-05-30 | 2013-12-05 | Devicor Medical Products, Inc. | Control for biopsy device |
| US20140039343A1 (en) | 2006-12-13 | 2014-02-06 | Devicor Medical Products, Inc. | Biopsy system |
| US8702623B2 (en) * | 2008-12-18 | 2014-04-22 | Devicor Medical Products, Inc. | Biopsy device with discrete tissue chambers |
| US9345457B2 (en) | 2006-12-13 | 2016-05-24 | Devicor Medical Products, Inc. | Presentation of biopsy sample by biopsy device |
| US7981049B2 (en) * | 2006-12-13 | 2011-07-19 | Devicor Medical Products, Inc. | Engagement interface for biopsy system vacuum module |
| US8480595B2 (en) * | 2006-12-13 | 2013-07-09 | Devicor Medical Products, Inc. | Biopsy device with motorized needle cocking |
| US8808200B2 (en) | 2007-10-01 | 2014-08-19 | Suros Surgical Systems, Inc. | Surgical device and method of using same |
| US8202229B2 (en) | 2007-10-01 | 2012-06-19 | Suros Surgical Systems, Inc. | Surgical device |
| US20090131819A1 (en) * | 2007-11-20 | 2009-05-21 | Ritchie Paul G | User Interface On Biopsy Device |
| US7858038B2 (en) * | 2007-11-20 | 2010-12-28 | Devicor Medical Products, Inc. | Biopsy device with illuminated tissue holder |
| US9039634B2 (en) * | 2007-11-20 | 2015-05-26 | Devicor Medical Products, Inc. | Biopsy device tissue sample holder rotation control |
| US7806835B2 (en) * | 2007-11-20 | 2010-10-05 | Devicor Medical Products, Inc. | Biopsy device with sharps reduction feature |
| US8052616B2 (en) * | 2007-11-20 | 2011-11-08 | Devicor Medical Products, Inc. | Biopsy device with fine pitch drive train |
| US20090131821A1 (en) * | 2007-11-20 | 2009-05-21 | Speeg Trevor W V | Graphical User Interface For Biopsy System Control Module |
| US8454531B2 (en) * | 2007-11-20 | 2013-06-04 | Devicor Medical Products, Inc. | Icon-based user interface on biopsy system control module |
| US8091455B2 (en) | 2008-01-30 | 2012-01-10 | Cummins Filtration Ip, Inc. | Apparatus, system, and method for cutting tubes |
| AU2009332945A1 (en) * | 2008-12-30 | 2011-07-07 | Biopath Automation, L.L.C. | Systems and methods for processing tissue samples for histopathology |
| CN102292030B (en) * | 2009-01-22 | 2014-11-19 | 比欧帕斯自动化公司 | Microtome sectionable biopsy support for orienting tissue samples |
| CN103830004A (en) | 2009-02-26 | 2014-06-04 | 斯特赖克公司 | Surgical tool arrangement having handpiece usable with multiple surgical tools |
| JP6101078B2 (en) | 2009-05-28 | 2017-03-29 | アビンガー・インコーポレイテッドＡｖｉｎｇｅｒ， Ｉｎｃ． | Optical coherence tomography for bioimaging |
| EP2691038B1 (en) | 2011-03-28 | 2016-07-20 | Avinger, Inc. | Occlusion-crossing devices, imaging, and atherectomy devices |
| US9254142B2 (en) | 2011-04-11 | 2016-02-09 | Iogyn, Inc. | Tissue extraction devices and methods |
| JP2014531224A (en) * | 2011-07-28 | 2014-11-27 | スパイン ビュー， インコーポレイテッド | Discectomy device and related methods |
| US9439720B2 (en) | 2011-09-01 | 2016-09-13 | Iogyn, Inc. | Tissue extraction devices and methods |
| US9808146B2 (en) | 2011-12-02 | 2017-11-07 | Interscope, Inc. | Endoscopic tool for debriding and removing polyps |
| US9439677B2 (en) | 2012-01-20 | 2016-09-13 | Iogyn, Inc. | Medical device and methods |
| US9827004B2 (en) | 2012-01-31 | 2017-11-28 | Globus Medical, Inc. | Surgical disc removal tool |
| US8585726B2 (en) | 2012-01-31 | 2013-11-19 | Globus Medical, Inc. | Surgical disc removal tool |
| US9232958B2 (en) | 2012-05-16 | 2016-01-12 | Smith & Nephew, Inc. | Reusable blade hub assembly |
| JP6046955B2 (en) * | 2012-08-28 | 2016-12-21 | マニー株式会社 | Vitreous surgery probe and method of manufacturing the same |
| WO2014093158A1 (en) * | 2012-12-12 | 2014-06-19 | Covidien Lp | Debulking catheter |
| US9839441B2 (en) | 2013-03-14 | 2017-12-12 | Stryker Corporation | Surgical tool arrangement and surgical cutting accessory for use therewith |
| WO2014143064A1 (en) | 2013-03-15 | 2014-09-18 | Avinger, Inc. | Chronic total occlusion crossing devices with imaging |
| US9636131B2 (en) | 2013-03-15 | 2017-05-02 | Stryker Corporation | Surgical tool arrangement and surgical cutting accessory for use therewith |
| EP2986229A4 (en) | 2013-04-16 | 2016-09-28 | Transmed7 Llc | Methods, devices and therapeutic platform for automated, selectable, soft tissue resection |
| AU2014265228B2 (en) | 2013-05-17 | 2015-12-24 | Interscope, Inc. | Insertable endoscopic instrument for tissue removal |
| JP6517198B2 (en) | 2013-07-08 | 2019-05-22 | アビンガー・インコーポレイテッドＡｖｉｎｇｅｒ， Ｉｎｃ． | Identification of elastic layers guiding interventions |
| WO2015143308A1 (en) | 2014-03-20 | 2015-09-24 | Medical Instrument Development Laboratories, Inc. | Aspirating cutter and method to use |
| CA2955242A1 (en) | 2014-07-08 | 2016-01-14 | Avinger, Inc. | High speed chronic total occlusion crossing devices |
| WO2016054064A2 (en) | 2014-09-30 | 2016-04-07 | Interscope, Inc. | Methods and apparatus for removing material from within a mammalian cavity using an insertable endoscopic instrument |
| WO2016054061A1 (en) | 2014-09-30 | 2016-04-07 | Interscope, Inc. | Endoscope including a torque generation component or torque delivery component disposed within an insertable portion of the endoscope and a surgical cutting assembly insertable within the endoscope |
| JP6392982B2 (en) | 2014-09-30 | 2018-09-19 | インタースコープ， インク．Ｉｎｔｅｒｓｃｏｐｅ， Ｉｎｃ． | Endoscope including a torque generating element or torque delivery element disposed within an insertable portion of an endoscope and a surgical cutting assembly insertable into the endoscope |
| WO2016054063A1 (en) | 2014-09-30 | 2016-04-07 | Interscope, Inc. | Endoscope including a torque generation component or torque delivery component disposed within an insertable portion of the endoscope and a surgical cutting assembly insertable within the endoscope |
| US10470786B2 (en) | 2014-10-16 | 2019-11-12 | Stryker Corporation | Surgical tool arrangement and surgical cutting accessory for use therewith |
| ES2919935T3 (en) | 2016-03-15 | 2022-07-29 | Interscope Inc | Surgical console, sample receiver and insertable endoscopic instrument for tissue extraction |
| US10433856B2 (en) * | 2016-07-11 | 2019-10-08 | Grace Medical, Inc. | Surgical drill handpiece with adjustable cutting tool guard |
| KR102563599B1 (en) * | 2016-10-26 | 2023-08-04 | 디. 스미스 마이클 | Portable surgical device with a rotating part |
| CN110505850B (en) | 2017-02-01 | 2022-10-28 | 因特斯高普公司 | Rotation control mechanism for outer sleeve of endoscope tool |
| EP3661435B1 (en) | 2017-08-02 | 2022-12-21 | Stryker Corporation | Surgical tool systems |
| JP7299918B2 (en) * | 2018-04-19 | 2023-06-28 | アビンガー・インコーポレイテッド | occlusion crossing device |
| JP7138921B2 (en) * | 2018-07-13 | 2022-09-20 | 公立大学法人福島県立医科大学 | surgical instruments |
| CN111345870B (en) * | 2018-12-24 | 2021-07-30 | 爱科凯能科技（北京）股份有限公司 | High-efficiency soft tissue planing device |
| US11622786B2 (en) * | 2019-03-27 | 2023-04-11 | Gyrus Acmi, Inc. | Planar alignment for asymmetric cutting members |
| US11883626B2 (en) | 2019-06-27 | 2024-01-30 | Boston Scientific Scimed, Inc. | Detection of an endoscope to a fluid management system |
Family Cites Families (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US2574066A (en) * | 1950-10-20 | 1951-11-06 | Samuel Briskman | Shears for producing zigzag cuts |
| US2721555A (en) * | 1952-12-03 | 1955-10-25 | John A Jenney | Dermatome |
| US3732858A (en) * | 1968-09-16 | 1973-05-15 | Surgical Design Corp | Apparatus for removing blood clots, cataracts and other objects from the eye |
| US3618611A (en) * | 1969-03-05 | 1971-11-09 | Julius C Urban | Vacuum rotary dissector |
| US4167943A (en) * | 1977-06-27 | 1979-09-18 | Surgical Design Corp. | Blade type rotatable surgical cutting instrument with improved cutter blade wear |
| US4203444A (en) * | 1977-11-07 | 1980-05-20 | Dyonics, Inc. | Surgical instrument suitable for closed surgery such as of the knee |
| US4368734A (en) * | 1978-01-27 | 1983-01-18 | Surgical Design Corp. | Surgical instrument |
| US4834729A (en) * | 1986-12-30 | 1989-05-30 | Dyonics, Inc. | Arthroscopic surgical instrument |
| US4850354A (en) * | 1987-08-13 | 1989-07-25 | Baxter Travenol Laboratories, Inc. | Surgical cutting instrument |
| JPH06114070A (en) * | 1990-06-22 | 1994-04-26 | Vance Prod Inc | Tissue abscission device for surgery |
-
1991
- 1991-02-14 US US07/655,035 patent/US5217479A/en not_active Expired - Fee Related
-
1992
- 1992-02-06 CA CA002060758A patent/CA2060758A1/en not_active Abandoned
- 1992-02-10 AU AU10828/92A patent/AU644265B2/en not_active Ceased
- 1992-02-13 EP EP92301181A patent/EP0499465A1/en not_active Withdrawn
- 1992-02-14 JP JP4027946A patent/JPH0595963A/en active Pending
Also Published As
| Publication number | Publication date |
|---|---|
| EP0499465A1 (en) | 1992-08-19 |
| US5217479A (en) | 1993-06-08 |
| AU1082892A (en) | 1992-08-20 |
| AU644265B2 (en) | 1993-12-02 |
| JPH0595963A (en) | 1993-04-20 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US5217479A (en) | Surgical cutting instrument | |
| US4844064A (en) | Surgical cutting instrument with end and side openings | |
| EP1176915B1 (en) | Percutaneous material removal device | |
| US4867157A (en) | Surgical cutting instrument | |
| US5084052A (en) | Surgical cutting instrument with plurality of openings | |
| US5964777A (en) | Surgical cutting instrument | |
| US4811734A (en) | Surgical cutting instrument | |
| US5007917A (en) | Single blade cutter for arthroscopic surgery | |
| US5376078A (en) | Rotatable surgical cutting instrument with positionally adjustable window | |
| US6001116A (en) | Endoscopic shaver blade with resilient cutting edges | |
| US5913867A (en) | Surgical instrument | |
| US6419684B1 (en) | End-cutting shaver blade for axial resection | |
| EP0651973B1 (en) | Surgical router | |
| US7641667B2 (en) | Tissue cutting instrument | |
| EP1676537A1 (en) | Surgical tool with cannulated rotary tip | |
| WO1994026181A1 (en) | Surgical cutting instrument | |
| EP0669105B1 (en) | Endoscopic resection instrument | |
| EP0556335A4 (en) | Surgical instrument for material removal | |
| AU768557B2 (en) | Surgical cutting instrument |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| FZDE | Discontinued | ||
| FZDE | Discontinued |
Effective date: 20000207 |