US3848276A - Knee implant device - Google Patents

Knee implant device Download PDF

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Publication number
US3848276A
US3848276A US00356816A US35681673A US3848276A US 3848276 A US3848276 A US 3848276A US 00356816 A US00356816 A US 00356816A US 35681673 A US35681673 A US 35681673A US 3848276 A US3848276 A US 3848276A
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United States
Prior art keywords
connector
joint
pivot
joint prosthesis
connector block
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Expired - Lifetime
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US00356816A
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English (en)
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Y Martinez
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Individual
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Individual
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Priority to US00356816A priority Critical patent/US3848276A/en
Priority to JP49049601A priority patent/JPS614538B2/ja
Priority to GB1955474A priority patent/GB1467727A/en
Priority to BE148501A priority patent/BE819892A/fr
Priority to US524708A priority patent/US3909854A/en
Application granted granted Critical
Publication of US3848276A publication Critical patent/US3848276A/en
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2/38—Joints for elbows or knees
    • A61F2/3836—Special connection between upper and lower leg, e.g. constrained
    • A61F2/384—Special connection between upper and lower leg, e.g. constrained hinged, i.e. with transverse axle restricting the movement
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2002/30001—Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
    • A61F2002/30621—Features concerning the anatomical functioning or articulation of the prosthetic joint
    • A61F2002/30624—Hinged joint, e.g. with transverse axle restricting the movement

Definitions

  • ABSTRACT A joint prosthesis particularly useful in total knee replacement, and capable of providing controlled motion about three axes corresponding to the capabilities of a normal knee.
  • a dual centered pivot with contacting arcuate support blocks provides' for a combination of rotational and translational movement during knee bending movements.
  • Axial rotation of the femur (upper leg) relative to the tibia (lower leg) is also possible through the normal range of movements, and a bias toward the neutral position is provided to signal the patient that such rotation exists.
  • Flexure or bending of the joint in an axis transverse to the normal knee axis is also provided with a resilient bias toward the aligned orientation.
  • the joint is secured to the bone structure by self tapping connector screws.
  • the connector screws are locked in place by outrigger screws.
  • the entire knee joint is enclosed in a flexible encapsulating cover to prevent damage to adjacent tissues and contamination of body fluids.
  • a knee prosthesis useful in total knee replacement that is relatively strong and stable, and which closely duplicates the rotational and translational constraints and capabilities of a normal knee.
  • Such a knee is particularly to be desired if it provides for attachment to the bone structure with the removal of a minimum amount of ligaments and other supportive tissue, and without substantial weakening of the bone structure. It is further desirable in such a knee that a natural feel be provided in those motions that result in resistance in the normal knee.
  • a still further desirable characteristic of such a knee is the protection of the body tissue surrounding the prosthesis from damage by contact with the moving parts and the exclusion of body fluids from the knee structure to avoid chemical contamination of the body or corrosive damage to the knee joint.
  • the pivot bearing comprises a pair of pivot pins carried in a pivot shield for supporting the structure of the apparatus.
  • Each pivot pin carries an arcuate support block with opposed arcuate surfaces in a combination of rolling and sliding contact during the knee bending function to produce the combined bending and translational movements.
  • a connector block is fitted over the pivot pins through an enlarged mounting opening having a curved surface and a flat surface. The enlarged opening provides for a degree of relative rotation between the upper leg and lower leg portions of the device.
  • the joint structure is secured to the bone structure in the case of a total knee prosthesis through self tapping screws and a bonded saddle.
  • the connector screw shape is a highly pitched undercut thread which may be screwed into the central portion of the femur and tibia to produce a sound support for the knee joint structure.
  • Three locking screws or outriggers are employed to lock the attaching screw and saddle in position and prevent loosening in use.
  • the connector block is pinned to the screw and the pin locked in place by a resiliently latched lock slide.
  • the joint structure is of a size that permits it to be installed within the confines of the original bone dimensions.
  • the bone is surgically configured to the exterior dimensions of upper and lower saddles.
  • the saddles are cemented in position.
  • the saddles replace the removed hard bone surface and thereby retain the monocoque reinforcing effect and maintain adequate structural strength.
  • the final motion provided for in the joint will be referred to as a tilting in the lateral plane of the joint, and is accomplished by mounting the connector screw to the pivot bearing through a connector pin.
  • the connector screw is held by the pin in a socket in a connector block.
  • the socket is filled by material having sufficient resiliency to permit the eight to ten degrees of tilting that duplicates that obtainable in normal knees.
  • the resilient material is the same silicone rubber or other flexible substance used in providing an encapsulation for the entire joint structure.
  • Encapsulating material is formed in two halves and joined to the pivot shield around the periphery at the central portion of the shield. The material is bonded to the metal to provide a permanent seal against the admission of body fluids.
  • Sufficient material is provided to form a fold on the front face of the knee to permit knee bending through the full travel desired.
  • the rear face is provided with paired opposed recesses to insure that the bending is always along the same line.
  • FIG. 1 is a side elevation view of a knee joint prosthesis with portions of the leg bones indicated in broken line.
  • FIG. 2 is a rear elevation view of the joint with portions of the flexible encapsulating material cut away.
  • FIG. 3 is a sectional view taken on line 33 of FIG. 2.
  • FIG. 4 is a sectional view taken on line 44 of FIG.
  • FIG. 5 is a sectional view taken on line 55 of FIG.
  • FIG. 6 is a sectional view taken on line 66 of FIG.
  • FIG. 7 is an enlarged prospective view of a connector pin and lock slide.
  • FIG. 8 is a side elevation view "partially cut away showing the bending action.
  • FIG. 9 is a sectional view taken on line 99 of FIG.
  • FIG. 10 is a sectional view similar to FIG. 9 showing v the rotational action.
  • the saddles have arcuate facing surfaces 23 and 25 to permit maximum bone contact without interference during knee bending actlon.
  • a pivot shield 26 mounts pivot pins 28 and 30 which are held in position through the pivot shield by retainers 32.
  • the pivot pins 28 and 30 carry upper and lower connector blocks 34 and 36.
  • the entire joint structure is encapsulated by a flexible encapsulation member 37 of silicone rubber including upper and lower portions 39 and 40.
  • pivot shield 26 which, at its rear facing edge, has a rear portion 44 of a peripheral channel to capture the locking portions of the upper and lower encapsulation members 39 and 40.
  • the front face of the pivot shield has the corresponding front portion 46 of the channel.
  • the pivot shield 26 has rear facing arcuate portions 50 and 52 which cooperate to stabilize the movements of the connector blocks as is described more fully hereinafter.
  • the upper and lower connector blocks 34 and 36 are identical and will be described by reference to connector block 34.
  • the connector block has an axial bore 54 for receiving the arcuate support block 60.
  • the arcuate support block 60 is constrained within the support block bore 54 to axial movement and is resiliently biased away from the bottom of the bore 54 by a spring washer 68 centered over a protrusion 64 on the support block.
  • the connector block 34 has channels 61 and 62 to provide attachment and bonding points for the encapsulation material 37 and a socket 58 which receives the connector screw 16.
  • the socket 58 has inclined sides as is best illustrated in FIG. 5 and therefore receives an excess amount of the silicone rubber 94 to provide for up to 10 degrees of tilting movement of the connector screw 16 relative to the connector block 34.
  • the connector screw 16 and block 34 are secured together by a connector pin 80, and the assembly retained in position by a lock slide 82.
  • a connector block slide is received around the lower portion of connector block 34.
  • The. slide 150 moves along the connector block when pressure is placed on the knee in the aligned position to accommodate movement of the roller blocks 60 in bore 54.
  • the connector block slide is carried on pin 28.
  • the surface 56 on slide 150 contacts the pivot shield inner surface 50 during approximately the first 20 degrees of bending in the joint, after which the surface 56 rotates out of contact to permit axial rotation.
  • the connector screw 16 has threads 86 which are highly undercut and have a pitch of approximately 37 so that the screw is self tapping.
  • the screw is held locked into the bone by a plurality of outriggers 20 which are secured in threaded bores near the end of the connector screw.
  • the connector screw carries a flange 17 which is received in a recess in the attachment pad 23 of the saddle 22.
  • Pad 23 of saddle 22 also includes a plurality of angulated bores 88 which receive the outrigger screws 20 and are aligned so as to position the outrigger screws for their eventual insertion into threads in the outer circumference of the connector screw 16.
  • the mounting of the screw results in the primary stress being transferred in tension and permits the use of caboneous siliconalloyed isotopic carbon with its desirable non-reactivity to the histology of the body.
  • the indentations 123 and 125 are substantially of flattened conical configuration. During bending the conical indentations 123 and 125 are contacted by the connector blocks 34 and 36. This contact pushes the indentations 123 and 125 outwardly and thereby provides extra silicone rubber substantially along a line connecting the apexes of the cones. The extra silicone rubber insures that the bend line will be regular and will be consistently along the same line.
  • the extra silicone rubber 94 filling in the sloping sides of socket 58 in the connector clock permits eight to ten degrees of relative rotation about pin 80.
  • the connector pin 80 is illustrated as including a dovetail portion 100 which cooperates with the dovetail portion 102 on the lock slide 82.
  • the lock slide is retained in position in the connector block slide recess 115 by the shoulder 106.
  • the shoulder 106 is held in an expended position by the wedge member 105.
  • the wedge member itself is held in axial position i by engagement with shoulders 107 on slide tumblers IMPLANTATION AND USE
  • the device of the invention would have an assembled pivot structure and bondedv encapsulation. However, the connector screws 16 and saddles 22 and 24 would be left disassembled.
  • the natural knee is surgically exposed and bone is removed from the femur and tibia to produce a cavity configuration corresponding to the exterior configuration for the upper and lower saddles 22 and 24.
  • the saddles are temporarily put in place and holes for the outrigger screws 20 are drilled in the bone structure by the use of the holes 88 as a guide.
  • the central bore for the connector screws 16 is also drilled at this time.
  • the saddles are removed and the connector screws turned into place.
  • the connector screws are highly pitched and are therefore self tapping in the soft central bone structure. With the screws in place, the saddles are positioned against the connector screw flanges l7 and cemented to the cavity in the bone structure using methyl methacrylate or similar cement.
  • pivot pin 80 is retained in position by the lock slide 82 which engages the dovetail portion 100 on pin 80.
  • the lock slide is retained in the connector block 34 by squeezing the lock slide with a special purpose tool and allowing the shoulder 106 to pass within the lock slide recess 115 in the connector block 34, and then releasing pressure on the tool to allow the shoulder 106 to engage the corresponding shoulder on the channel in the lock slide recess 115.
  • the lock slide 82 is fixed against removal by the installation of the wedge member 105 which engages the shoulders 107 on the end tumblers 109 when it is fully inserted.
  • the incision When the installation is complete, the incision may be closed.
  • the post operative recuperative period is minimized by the fact that minimum tissue damage takes place during the operation.
  • the bone structure grows in and around all of the undercut threads on the connector screws 16, and in and around the outrigger screws 20. Thus a firm connecting support to the sound bone structure is provided.
  • the saddles 23 and 24 also transfer load to the bone through the cemented surfaces which heal rapidly.
  • the joint After recuperation, the joint is ready to operate in a manner closely approximating the natural knee joint.
  • FIG. 3 illustrates the erect knee position. It will be noted that the flat end surfaces of the roller blocks 60 are in contact, and that the surfaces 56 on the connector blocks contact the curved inner faces and 52 of the pivot shield 26. Thus the knee is locked. Rotational and other loads are transferred without joint movement.
  • FIG. 8 the configuration of the knee v bending is illustrated.
  • the surface 56 is now out of contact with the curved inner face 52 of the pivot shield.
  • the rotation of the surface 56 away from the pivot shield 26 pennits relative axialrotation of the tibia and femur, such as takes place in normal knees after approximately 20 degrees of bending. Rotation is accommodated on the curved arcuate surface 122 of enlarged opening 120.
  • FIG. 10 illustrates the relative position of the pivot pin 28 relative to the connector block 36 during joint rotation.
  • FIG. 11 is illustrative of the effect of rotation on the spring washer 68.
  • the pivot pin 28 is shown as rotating along the arcuate surface 122 so that it is out of contact with the very bottom portion thereof, and is positioned midway in the axial length of the opening 120. A total of .plus or minus 20 degrees is provided.
  • the spring washer 68 is partially compressed thereby creating a bias and giving the user a positional reference whereby a resistance sensation is produced corresponding with knee rotation.
  • the socket 58 which has sloping sides to accommodate extra silicone rubber 94.
  • the rubber serves to provide a positional sensation to the user during the lateral flexing action in a manner similar to that employed in axial rotation.
  • the entire mechanism is encased in the encapsulation 37 thereby excluding the tissues and fluids from the mechanism and preventing contact or possible pinching between any of the moving parts.
  • the encapsulation serves as a surface on which the patella may slide so that the important patellar functions are retained.
  • the action of the encapsulation during bending is illustrated in FIG. 8 wherein the folds 43 are partially extended and the folds are being created in the rear face of the encapsulation pairs 39 and- 40 along a regular bend line under the influence of indentations 123 and 125. With maximum knee extension the connector blocks will contact the rear portion of the pivot shield 26 limiting the total travel to the selected figure of approximately l35.
  • FIG. 8 also illustrates that during bending, contact is maintained between the roller surfaces and therefore extra stability is provided in the movement.
  • a joint prosthesis comprising:
  • attachment means for securing said joint means between relatively movable skeletal members
  • said joint means for constraining said skeletal members to a combination of relative rotation and translation
  • said joint means comprising at least two axially spaced pivot bearings incorporating two pivot pins, a common pivot frame, and two connector blocks,
  • pivot bearings being connected to said attachment means through said connector blocks,
  • said connector blocks having an axial bore and receiving said pivot pins through a transverse open ing through said axial bore.
  • said transverse opening in said connector block is enlarged to provide a limited pivoting freedom of movement for said pivot pins in said connector block.
  • said attachment means comprise a connector screw and each connector block is secured to said connector screw by a connector screw pivot pin received in a transverse bore through said connector screw and in said connector block.
  • said axial socket having radially opposed sloping sides
  • said opposed roller blocks having a face-to-face contact in the axially aligned orientation for said joint means, and having curved surfaces in contact during bending movement of said knee.
  • said connector block includes an arcuate surface which contacts the inner face of said pivot frame in the axially aligned orientation of said joint means
  • said arcuate surface on said connector block being pivotally moved away from said inner face after a pre-determined amount of bending in said joint means to allow limited relative axial rotation.
  • said arcuate surface sccommodates relative axial rotation of plus or minus 20.
  • said connector blocks have slide portions around the inner ends of said connector blocks.
  • said slide portions accommodating limited relative axial translation between said connector block and said slide.
  • attachment means comprising a connector screw adapted to be threaded into the interior axial portion of said skeletal members
  • outrigger screws threaded into said connector screw near the terminal end thereof at an acute angle to the longitudinal axis of saidconnector screw and adapted to pass through bone of said skeletal members.
  • an attachment system comprising a pair of saddle means comprising substantially U-shaped saddle members with an attachment pad atthe base of said U-shaped saddle members,
  • said saddle means adapted to be cemented to bone structure and secured to said joint mechanism through said attachment pad
  • said bores having an axis at an acute angle to the axis of a central bore through said attachment pad.
  • Apparatus for use in a joint prosthesis comprising:
  • said joint means comprising at least two spaced pivot bearings
  • pivot bearings comprising pivot pins carrying, for rotation, upper and lower connector block means
  • said connector block receives said connector screw in a socket with inclined sides to accommodate up to 10 of tilting movement.

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  • Health & Medical Sciences (AREA)
  • Orthopedic Medicine & Surgery (AREA)
  • Physical Education & Sports Medicine (AREA)
  • Cardiology (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Transplantation (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Vascular Medicine (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Prostheses (AREA)
US00356816A 1973-05-03 1973-05-03 Knee implant device Expired - Lifetime US3848276A (en)

Priority Applications (5)

Application Number Priority Date Filing Date Title
US00356816A US3848276A (en) 1973-05-03 1973-05-03 Knee implant device
JP49049601A JPS614538B2 (fr) 1973-05-03 1974-05-02
GB1955474A GB1467727A (en) 1973-05-03 1974-05-03 Knee joint prosthesis
BE148501A BE819892A (fr) 1973-05-03 1974-09-13 Dispositif pour le remplacement du genou
US524708A US3909854A (en) 1973-05-03 1974-11-18 Knee implant prosthesis

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
US00356816A US3848276A (en) 1973-05-03 1973-05-03 Knee implant device

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Publication Number Publication Date
US3848276A true US3848276A (en) 1974-11-19

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US00356816A Expired - Lifetime US3848276A (en) 1973-05-03 1973-05-03 Knee implant device

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US (1) US3848276A (fr)
JP (1) JPS614538B2 (fr)
BE (1) BE819892A (fr)
GB (1) GB1467727A (fr)

Cited By (35)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3990116A (en) * 1974-10-17 1976-11-09 Fixel Irving E Pretensioned prosthetic device for skeletal joints
US4092740A (en) * 1975-10-03 1978-06-06 Salomao Eshriqui Articulated joint prosthesis
US4187559A (en) * 1975-04-04 1980-02-12 Sybron Corporation Body joint endoprosthesis
US4267608A (en) * 1978-10-04 1981-05-19 Bora Jr F William Prosthetic joint
WO1983002555A1 (fr) * 1982-01-21 1983-08-04 Us Medical Corp Fixation de prothese sur l'os
US4462120A (en) * 1981-07-06 1984-07-31 Andre Rambert Total knee prosthesis
US4549319A (en) * 1982-08-03 1985-10-29 United States Medical Corporation Artificial joint fixation to bone
US4624673A (en) * 1982-01-21 1986-11-25 United States Medical Corporation Device system for dental prosthesis fixation to bone
US4634444A (en) * 1984-02-09 1987-01-06 Joint Medical Products Corporation Semi-constrained artificial joint
EP0274094A1 (fr) * 1987-01-03 1988-07-13 Manfred Dr. Kallabis Endoprothése sans ciment
US4828031A (en) * 1987-10-13 1989-05-09 Chevron Research Company In situ chemical stimulation of diatomite formations
US5176709A (en) * 1989-04-25 1993-01-05 Medevelop Ab Method for inserting an anchoring element within a bone
US5534031A (en) * 1992-01-28 1996-07-09 Asahi Kogaku Kogyo Kabushiki Kaisha Prosthesis for spanning a space formed upon removal of an intervertebral disk
US5755807A (en) * 1996-06-17 1998-05-26 Folsom Metal Products Implant module unit and rotating seal for prosthetic joint
US5984970A (en) * 1996-03-13 1999-11-16 Bramlet; Dale G. Arthroplasty joint assembly
US6503280B2 (en) 2000-12-26 2003-01-07 John A. Repicci Prosthetic knee and method of inserting
US6695844B2 (en) 1996-03-13 2004-02-24 Orthopedic Designs, Inc. Surgical fastener assembly
US20120150309A1 (en) * 2009-04-29 2012-06-14 Roelof Marissen Hinge structure
US20150265409A1 (en) * 2012-07-17 2015-09-24 Clemson University Research Foundation Lockable knee implants and related methods
US9254130B2 (en) 2011-11-01 2016-02-09 Hyun Bae Blade anchor systems for bone fusion
US9480511B2 (en) 2009-12-17 2016-11-01 Engage Medical Holdings, Llc Blade fixation for ankle fusion and arthroplasty
US9615856B2 (en) 2011-11-01 2017-04-11 Imds Llc Sacroiliac fusion cage
US9925051B2 (en) 2010-12-16 2018-03-27 Engage Medical Holdings, Llc Arthroplasty systems and methods
CN107898537A (zh) * 2017-11-09 2018-04-13 赵玉芯 一种骨关节假体平台垫片组件
US10238382B2 (en) 2012-03-26 2019-03-26 Engage Medical Holdings, Llc Blade anchor for foot and ankle
US10390955B2 (en) 2016-09-22 2019-08-27 Engage Medical Holdings, Llc Bone implants
US10456272B2 (en) 2017-03-03 2019-10-29 Engage Uni Llc Unicompartmental knee arthroplasty
US20210267764A1 (en) * 2020-02-28 2021-09-02 Extensor, LLC Implantable Knee Prosthesis with Integrated Prosthetic Extensor Mechanism.
US20220265333A1 (en) * 2021-02-09 2022-08-25 Rtg Scientific, Llc Arthroplasty implants, systems, and methods
US11540928B2 (en) 2017-03-03 2023-01-03 Engage Uni Llc Unicompartmental knee arthroplasty
WO2023215419A1 (fr) * 2022-05-04 2023-11-09 Rtg Scientific, Llc Implants et systèmes d'arthroplastie
US11883081B2 (en) 2020-11-19 2024-01-30 Rtg Scientific, Llc Fastening devices, systems, and methods
US12121271B2 (en) 2021-02-09 2024-10-22 Rtg Scientific, Llc Femoral fixation devices, systems, and methods
US20240350268A1 (en) * 2019-07-15 2024-10-24 Evalve, Inc. Independent Proximal Element Actuation Methods
US12290292B2 (en) 2021-08-10 2025-05-06 Rtg Scientific, Llc Bone fixation devices, systems, methods, and instruments

Families Citing this family (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS59138939A (ja) * 1983-01-31 1984-08-09 Rikagaku Kenkyusho 物体の表面温度に対する温度感覚の定量検知方法とその装置

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3683421A (en) * 1970-07-13 1972-08-15 Skf Ind Inc Prosthetic joint assembly
US3708805A (en) * 1969-12-24 1973-01-09 Nat Res Dev Prosthetic elbow joint
US3739403A (en) * 1970-10-09 1973-06-19 F Nicolle Prosthetic joint having a tissue ingrowth preventive capsule
US3765033A (en) * 1971-01-19 1973-10-16 D Goldberg Prosthetic knee joint assembly with mutually slidable and rollable joint sections

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3708805A (en) * 1969-12-24 1973-01-09 Nat Res Dev Prosthetic elbow joint
US3683421A (en) * 1970-07-13 1972-08-15 Skf Ind Inc Prosthetic joint assembly
US3739403A (en) * 1970-10-09 1973-06-19 F Nicolle Prosthetic joint having a tissue ingrowth preventive capsule
US3765033A (en) * 1971-01-19 1973-10-16 D Goldberg Prosthetic knee joint assembly with mutually slidable and rollable joint sections

Cited By (50)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3990116A (en) * 1974-10-17 1976-11-09 Fixel Irving E Pretensioned prosthetic device for skeletal joints
US4187559A (en) * 1975-04-04 1980-02-12 Sybron Corporation Body joint endoprosthesis
US4092740A (en) * 1975-10-03 1978-06-06 Salomao Eshriqui Articulated joint prosthesis
US4267608A (en) * 1978-10-04 1981-05-19 Bora Jr F William Prosthetic joint
US4462120A (en) * 1981-07-06 1984-07-31 Andre Rambert Total knee prosthesis
WO1983002555A1 (fr) * 1982-01-21 1983-08-04 Us Medical Corp Fixation de prothese sur l'os
US4624673A (en) * 1982-01-21 1986-11-25 United States Medical Corporation Device system for dental prosthesis fixation to bone
US4549319A (en) * 1982-08-03 1985-10-29 United States Medical Corporation Artificial joint fixation to bone
US4634444A (en) * 1984-02-09 1987-01-06 Joint Medical Products Corporation Semi-constrained artificial joint
EP0274094A1 (fr) * 1987-01-03 1988-07-13 Manfred Dr. Kallabis Endoprothése sans ciment
US4828031A (en) * 1987-10-13 1989-05-09 Chevron Research Company In situ chemical stimulation of diatomite formations
US5176709A (en) * 1989-04-25 1993-01-05 Medevelop Ab Method for inserting an anchoring element within a bone
US5534031A (en) * 1992-01-28 1996-07-09 Asahi Kogaku Kogyo Kabushiki Kaisha Prosthesis for spanning a space formed upon removal of an intervertebral disk
US5776196A (en) * 1992-01-28 1998-07-07 Asahi Kogaku Kogyo Kabushiki Kaisha Prosthesis for spanning a space formed upon removal of an intervertebral disk
US6695844B2 (en) 1996-03-13 2004-02-24 Orthopedic Designs, Inc. Surgical fastener assembly
US5984970A (en) * 1996-03-13 1999-11-16 Bramlet; Dale G. Arthroplasty joint assembly
US6475242B1 (en) 1996-03-13 2002-11-05 Dale G. Bramlet Arthroplasty joint assembly
US5755807A (en) * 1996-06-17 1998-05-26 Folsom Metal Products Implant module unit and rotating seal for prosthetic joint
US6726724B2 (en) 2000-12-26 2004-04-27 John A. Repicci Prosthetic knee
US6503280B2 (en) 2000-12-26 2003-01-07 John A. Repicci Prosthetic knee and method of inserting
US20120150309A1 (en) * 2009-04-29 2012-06-14 Roelof Marissen Hinge structure
US9480511B2 (en) 2009-12-17 2016-11-01 Engage Medical Holdings, Llc Blade fixation for ankle fusion and arthroplasty
US10238426B2 (en) 2009-12-17 2019-03-26 Engage Medical Holdings, Llc Blade fixation for ankle fusion and arthroplasty
US11197763B2 (en) 2010-12-16 2021-12-14 Engage Medical Holdings, Llc Arthroplasty systems and methods
US10342667B2 (en) 2010-12-16 2019-07-09 Engage Medical Holdings, Llc Arthroplasty systems and methods
US9925051B2 (en) 2010-12-16 2018-03-27 Engage Medical Holdings, Llc Arthroplasty systems and methods
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JPS5027395A (fr) 1975-03-20
GB1467727A (en) 1977-03-23
JPS614538B2 (fr) 1986-02-10

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