WO2011104353A1 - Partie fémorale d'une prothèse de hanche, ainsi que prothèse de hanche - Google Patents

Partie fémorale d'une prothèse de hanche, ainsi que prothèse de hanche Download PDF

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Publication number
WO2011104353A1
WO2011104353A1 PCT/EP2011/052832 EP2011052832W WO2011104353A1 WO 2011104353 A1 WO2011104353 A1 WO 2011104353A1 EP 2011052832 W EP2011052832 W EP 2011052832W WO 2011104353 A1 WO2011104353 A1 WO 2011104353A1
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WO
WIPO (PCT)
Prior art keywords
shaft
axis
thigh part
widening
part according
Prior art date
Application number
PCT/EP2011/052832
Other languages
German (de)
English (en)
Inventor
Susanne Rabenseifner
Curt Kranz
Emmanuel Anapliotis
Original Assignee
Merete Medical Gmbh
Priority date (The priority date 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 date listed.)
Filing date
Publication date
Application filed by Merete Medical Gmbh filed Critical Merete Medical Gmbh
Publication of WO2011104353A1 publication Critical patent/WO2011104353A1/fr

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Classifications

    • 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
    • A61F2/32—Joints for the hip
    • A61F2/36—Femoral heads ; Femoral endoprostheses
    • A61F2/3662—Femoral shafts
    • 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
    • A61F2002/30108—Shapes
    • A61F2002/3011—Cross-sections or two-dimensional shapes
    • A61F2002/30159—Concave polygonal shapes
    • A61F2002/30161—Concave polygonal shapes arrow-shaped
    • 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
    • A61F2002/30108—Shapes
    • A61F2002/3011—Cross-sections or two-dimensional shapes
    • A61F2002/30159—Concave polygonal shapes
    • A61F2002/30172—T-shaped
    • 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
    • A61F2002/30108—Shapes
    • A61F2002/30199—Three-dimensional shapes
    • A61F2002/30308—Three-dimensional shapes banana-shaped
    • 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
    • A61F2/30767—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth
    • A61F2/30771—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth applied in original prostheses, e.g. holes or grooves
    • A61F2002/30878—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth applied in original prostheses, e.g. holes or grooves with non-sharp protrusions, for instance contacting the bone for anchoring, e.g. keels, pegs, pins, posts, shanks, stems, struts
    • A61F2002/30884—Fins or wings, e.g. longitudinal wings for preventing rotation within the bone cavity
    • 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
    • A61F2/32—Joints for the hip
    • A61F2/36—Femoral heads ; Femoral endoprostheses
    • A61F2/3662—Femoral shafts
    • A61F2002/3678—Geometrical features
    • A61F2002/3686—Geometrical features bent
    • 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
    • A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2230/0002—Two-dimensional shapes, e.g. cross-sections
    • A61F2230/0028—Shapes in the form of latin or greek characters
    • 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
    • A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2230/0002—Two-dimensional shapes, e.g. cross-sections
    • A61F2230/0028—Shapes in the form of latin or greek characters
    • A61F2230/0052—T-shaped
    • 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
    • A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2230/0063—Three-dimensional shapes

Definitions

  • the present invention relates to a femoral part of a hip joint prosthesis with a shaft and with a connection region, wherein the shaft is provided for insertion into a thigh bone and has a longitudinal direction along a longitudinal axis substantially, at an angle to the longitudinal axis of the shaft at the connecting portion is arranged, which serves for the mechanical connection of the shaft with a ball joint.
  • hip joint prostheses which produce an artificial connection of the femur with the hip joint as far as possible adaptation to anatomical conditions.
  • hip joint prostheses usually consist of a thigh part, which is to be attached to the femur or inserted into this. To the thigh part is followed by a ball joint on a connection area, the ball socket is to be fixed in the hip.
  • hip endoprosthetics it is generally possible to anchor the prosthesis cemented or cement-free in the bone. Both options have advantages and disadvantages from a medical point of view, so that they can initially be regarded as equivalent.
  • a decision as to whether a prosthesis is to be fastened by means of a cemented or cementless anchoring is to be decided by the surgeon intraoperatively on the basis of the available bone quality.
  • Conventional anatomically shaped endoprosthesis systems allow the use of cemented as well as cementless anchoring only in exceptional cases. There is therefore a need for hip arthroplasty, which can be used both cemented and cementless, the decision on the type of attachment to the surgeon should be reserved.
  • hip endoprosthetics has the disadvantage that, if appropriate, relatively much bone has to be removed in the proximal region of the trochanter in order to be able to introduce the thigh part.
  • the diameter of the distal shaft of the thigh part is often designed to be relatively large in relation to its proximal shaping, so that a bone thickness minimization is also necessary here for the insertion of the thigh part.
  • Various designs for hip joint prostheses are known from the patent literature. It discloses the US 3,067,740 a hip joint prosthesis, which has a shaft to which a connecting element is screwed for securing a ball joint.
  • a disadvantage of this hip joint prosthesis is the inadequate adaptation to the anatomy, whereby the removal of unnecessary bone material is required when inserting the prosthesis, which consequently leads to a weakening of the remaining bone.
  • a prosthesis for anchoring in a skeletal bone which is curved for anatomical adaptation in one direction and has a surface area which is provided with cutting edges.
  • the cutting edges cause a bone removal during insertion of the prosthesis, so that it comes due to the relatively simple design also to an at least partially bone weakening.
  • a thigh part of a hip joint prosthesis which is also curved in one direction and which has a double shoulder to increase the area for the introduction of forces in the bone. Because of the simply configured double shoulder, the removal of the prosthesis into the thighbone requires the removal of further bone material, in particular of softer central bone material. This leads to an additional weakening of the bone, in particular if the thigh part is pushed into the bone with a movement in one plane.
  • the present invention is therefore based on the object to provide a thigh part of a hip joint prosthesis as well as a hip joint prosthesis itself available, which have an optimum primary and final strength in the bone with the least possible weakening of the bone due to an optimal adaptation to the anatomical conditions.
  • a thigh part of a hip joint prosthesis with a shaft and a connecting region wherein the shaft is provided for insertion in a femur and has a longitudinal direction along a longitudinal axis, and at an angle to the longitudinal axis of the shaft at the connecting region is arranged, the mechanical connection of the Shank with a ball joint is used, wherein the femoral part is curved by a second axis, which runs substantially perpendicular to the longitudinal axis by the angled arrangement of the connecting portion.
  • the femoral part is also bent about a third axis which is substantially perpendicular to the longitudinal axis and perpendicular to the second axis.
  • At least one broadening is arranged on the region curved and convexly formed about the second axis. This broadening serves to increase the area with which pressure is exerted by the prosthesis on the bone or a bone cement, and thus to avoid damaging transverse forces.
  • the angle between the connection region and the longitudinal axis is between 120 ° and 150 °, preferably about 135 °.
  • the curvature about the second axis does not necessarily have a smooth course in the curved around the second axis concave area.
  • the concave area can also be formed from individual, linearly extending areas or flat areas, whose edges or corner points, however, form an overall curved and smooth area in the case of higher-grade interpolation.
  • the curved portion is concave toward the second axis side and convexly curved on the opposite side from the second axis.
  • the bending of the femoral part about the third axis also denotes a curvature which, however, does not necessarily have to be produced by a bending process but can also be produced by a primary molding process.
  • the orientation of the individual axes to each other is preferably perpendicular.
  • the curvature of the femoral portion about the third axis has the advantage of improved adaptation to the human anatomy such that as the femoral stem is inserted into a femur, less material must be removed at the femur and especially at the proximal portion of the trochanter. This has an overall effect of increasing the stability on the bone provided with the endoprosthesis.
  • the thigh part according to the invention can be used both for the cement-free and for the cemented implantation. It is thus an anatomically adapted prosthesis. Optimal forces and moments can be transmitted from the hip to the thigh bone due to the maximum adaptation of the shape between the force-absorbing bone bearing and the force-introducing implant. In doing so, it is also possible to absorb load peaks or unfavorable force discharges from the prosthesis in an excellent manner and to transfer them into the thigh part in such a way that it is loaded in an optimum manner.
  • the present femoral part of the hip prosthesis in addition to a maximum bony congruence, taking into account the anteversion and the connection between femoral shaft and Femurmethaphyse or femoral neck called helitorion another has functional congruence, which may also be referred to as soft tissue congruence.
  • This soft tissue congruence receives the thigh part according to the invention by the optimal adaptation to the biological conditions, especially in the thighbone.
  • the adaptation is achieved, in particular, by the combination of the bends around the second and third axes with the at least one widening, which essentially follows the bends of the thigh part, in particular the bend around the third axis. This allows a uniform bias of the hip stabilizing and moving muscle and ligaments realize.
  • permanently harmful micro-movements of the proximal end are avoided, which can lead to a weakening of the bone.
  • an intermediate region is arranged between the shank and the broadening, which in sections causes a greater depth of the shank in the direction parallel to the third axis than the depth of the shank at its distal end.
  • the shaft has a round cross-section at its distal end, but in the region of the intermediate region and the broadening in the direction of the depth, a cross-section deviating from the round shape.
  • a step is formed between the broadening and the intermediate area.
  • the intermediate region preferably runs continuously in the direction of the distal end of the shaft towards the shaft. That is, there is no edge between the lip of the intermediate region and the distal end of the stem.
  • a widening is arranged on both sides of the intermediate region, which together form a double shoulder. That is, the direction of the width of the spacers is that corresponding to the second axis. Regardless of their number, apart from the increase in area, the widenings serve to induce the weight of the patient over the thigh part in the femur or in the thigh bone with an optimum primary rotational stability.
  • the intermediate region runs continuously to the distal end of the shaft on the shaft, run or run the one or both extensions to the distal end of the shaft out.
  • the broadening on the side facing away from the second axis is also convexly curved, wherein the radius of curvature of the convex curvature of the broadening is less than the radius of curvature of the concave curvature of the shank about the second axis. That is, the approximate radii centers of both convexes are at different positions.
  • the broadening has a convex curvature about an axis extending substantially parallel to the longitudinal axis. In this case, this axis is preferably not arranged directly on the longitudinal axis, so that the convex curvature of the widening is not symmetrical with respect to the longitudinal axis.
  • the shaft is configured from its distal end to the beginning of broadening substantially frusto-conical.
  • This truncated cone has an angle of 0.8 ° to 2.4 °.
  • the convexity of the broadening about the second axis is such that this convex portion is at least partially spaced a greater distance from the longitudinal axis of the stem than the maximum distance of the surface of the stem from its longitudinal axis of the distal and substantially minor truncated cone portion of the stem ,
  • the distance of the convex portion from the longitudinal axis is based on an ideal and linear longitudinal axis of the femoral part.
  • the broadening on the side of the shaft concavely curved about the third axis is likewise concavely curved, and the broadening on the side of the shaft convexly curved about the third axis is essentially linear. That is, the double shoulder on the concave side substantially follows the curvature of the shaft about the third axis, but not on the convex side.
  • a cone is preferably connected for receiving a ball of a ball joint.
  • This cone preferably has at least one transverse groove for the mechanical locking of the ball.
  • This transverse groove or the groove running on the circumference of the cone ensures a firm mechanical connection of the thigh part with a detachable ball head, which preferably consists of ceramic or metal.
  • the connecting region preferably tapers in the direction of the cone. This taper requires a weight saving of the thigh part while ensuring the mechanical stability.
  • the thigh part has a surface roughness Rz at least in the third of the shaft arranged at the proximal end of at least 63 ⁇ .
  • a hip joint prosthesis with a thigh part according to the invention and with a ball of a ball joint is also provided.
  • the thigh member according to the invention thus has substantially curvatures which have no inflection points.
  • the thigh part can be made of solid material or hollow material and be used with or without cement in the bone. This means that the thigh part can be cemented or cement-free anchored with the same instruments.
  • the surgeon has the choice between preferably eight cementless prosthesis sizes for the left and right side. This significantly improves anatomical adaptation to the diaphysis and avoids unnecessary drilling of the canal. Due to the adaptation to the natural anatomical shape of the femur, significantly less bone material has to be removed than is the case with conventional prostheses.
  • the same rasps must be used for the cementless as well as the cemented fixation of the thigh part.
  • the thickness of the cement layer in cemented prostheses is defined by the choice of prosthesis size, which is smaller than the rasp size.
  • Suitable materials are titanium or suitable titanium alloys, such as Ti 6 Al 4 V, which are preferably forged.
  • the invention has a slimmer shape of the distal third and a rounding of the prosthesis shoulder to obtain the spongy structures in the trochanter major area.
  • An improvement of the rotational stability is effected by a ventral and dorsal step for improved introduction of force.
  • the advantage of minimizing bone decay on the proximal femur is provided by anatomical adaptations, consistent proximal application of force, and avoidance of distal bone remodeling.
  • the thigh part according to the invention or the hip joint prosthesis comprising this thigh part can be implanted in such a way that the femur is rasped up and thus produces a cavity in the femur that is at least complementary in shape to the shaft of the thigh part.
  • the medullary cavity openings should only be reamed to the extent required by a straight stem prosthesis.
  • the shaft of the thigh part of the prosthesis is preferably to be inserted manually and then with a few punches with a Einschlagaginstrument.
  • An anatomical placement of the implant is accompanied by a slight final rotation, after which a primary stability arises.
  • the prosthesis is to be driven in with further solid punches. It can be cemented, for which a larger cavity must be grated than when inserting without cementing.
  • connection with the ball joint takes place in such a way that either the ball is already arranged on the thigh part and is to be inserted into a ball socket, or that the thigh part is to be connected to a ball inserted in a ball socket.
  • the advantage of this implantation procedure is that no disruptions or perforations of the bone shaft are to be expected and no trochanter tear.
  • a cement-free anchored shaft ensures both the anatomical shape of the shaft and the special surface texture optimal fit and thus supports the biomechanical concept of long-term anchorage.
  • the joint forces are thereby optimally introduced into the bony structure of the femur and thus promotes a growth of the bone cells.
  • the center of gravity of the hip is restored and therewith also a physiological muscle and ligament tension. Both ensure a very good and safe hip mobility already shortly after the operation.
  • the femoral component When the femoral component is to be cemented, it is to be implanted in a closed cement jacket in the medullary cavity of the femur.
  • the design of the prosthesis stem is tuned to an optimal support in the bone cement.
  • This composite holds the prosthesis stem and, under load, safely introduces the force into the thighbone.
  • the Hsymmetric searchtician is restored and a uniform muscle and ligament tension realized, so that even here a very good hip mobility is already guaranteed shortly after surgery.
  • the thigh part according to the invention and the hip joint prosthesis can be provided in a left and in a right variant, which are configured in mirror image to each other.
  • the invention will be described below with reference to the accompanying drawings. It shows: a thigh part according to the invention in a perspective view, a thigh part according to the invention in front view, a thigh part according to the invention in a view from the side, and
  • the thigh part 1 essentially comprises a shaft 10, which has a distal end 11 and a proximal end 12.
  • the thigh part 1 essentially has a longitudinal extension direction 13 along a longitudinal axis 14.
  • the longitudinal axis 14 is substantially the axis of symmetry of the distal end 1 1 of the shaft 10.
  • an intermediate portion 40 is arranged, in the direction of the depth of the thigh part 1, a first broadening 30 and join a second broadening 31, which together form a so-called double shoulder.
  • a connecting region 60 connects, which leads to a cone 70.
  • This cone 70 serves to receive a ball joint.
  • At the cone 70 can be arranged not shown transverse grooves for the purpose of mechanical attachment of the ball.
  • the thigh part 1 is curved about a second axis 15.
  • This second axis 15 preferably extends perpendicular to the longitudinal axis 14.
  • the curvature of the femoral part 1 about the second axis 15 can be seen.
  • the proximal end 12 of the shaft 10 has a concave curvature 19. This concave curvature is created by the rounding of the angle 17 between the cone 70 and the longitudinal axis 14 or the distal end 11.
  • the invention is not necessarily It may alternatively be provided that, instead of the concave curvature 19, a multiplicity of flat surfaces are arranged which, despite the formation of connecting edges, realize an anatomical adaptation of the thigh part to the femur.
  • the thigh part 1 Due to the arrangement of the intermediate region 40 between the widenings 30, 31 and the concave curvature 19, the thigh part 1 has an enlarged depth of the shank 50 in this region.
  • the first and the second widening 30, 31 do not run linearly, but are also curved about the second axis 15, so that they also have a convex curvature 51.
  • this convex curvature 51 of the spacers 30, 31 has a smaller radius of curvature about the second axis 52 than the radius of curvature of the curvature of the shank about the second axis 53, whose curvature is substantially parallel to the concave curvature 19.
  • the arrangement of the intermediate region 40 and the angle 17 results in a step 18 between the connection region 60 and the intermediate region 40 or widenings 31, 32.
  • the spacers 31, 32 approach in a stepless spout 41 to the distal end 1 1 of the shaft 10 at.
  • the shaft 10 in the direction of the distal end 1 1 preferably has a truncated cone shape, which is defined by the cone angle 55.
  • the distal end forms a spherical segment.
  • the shaft 10 is configured such that the maximum distance 56 of the convex portion 51 of the widening elements 31, 32 to the longitudinal axis 14 is greater than the maximum distance 57 of the surface of the frusto-conical shaft to the longitudinal axis 14.
  • This embodiment of the shape requires excellent end stability. As can be seen in particular from FIG.
  • the thigh part 1 not only has a curvature about the second axis 15, but also a curvature about a third axis 16. That is to say, the thigh part 1 is bent two-dimensionally. In this case, it has the peculiarity that the first widening 30 by the bend about the third axis 16 also has a concave curvature 58 about the third axis 16. However, the second widening 31 has a linear course 59.
  • This embodiment also serves, in particular, to produce an excellent initial stability as well as good end stability of the prosthesis.
  • the double shoulder realized by the first broadening 30 and the second broadening 31 additionally has a convex curvature 54 around a plane parallel to the longitudinal axis 14 Axle up.
  • This axis, around which the convex curvature of the spacers 30, 31 is realized is preferably not the longitudinal axis 14 itself, but is at a distance therefrom, so that the convex curvature 54 is asymmetrical with respect to the longitudinal axis 14. It can be seen from FIG. 4 that the connecting region 60 between the widenings 30, 31 and the cone 70 tapers in the direction of the cone 70.

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  • Health & Medical Sciences (AREA)
  • Orthopedic Medicine & Surgery (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)

Abstract

L'invention concerne une partie fémorale d'une prothèse de hanche comprenant une tige et une zone de raccordement, la tige étant prévue pour le placement dans un fémur et présentant essentiellement un sens d'extension longitudinale le long d'un axe longitudinal, et la zone de raccordement étant disposée sur la tige sous un angle par rapport à l'axe longitudinal de la tige, ladite zone de raccordement servant à l'assemblage mécanique de la tige avec une articulation à bille. Grâce à la disposition sous un angle de la zone de raccordement, la partie fémorale est courbée autour d'un deuxième axe, qui s'étend de manière essentiellement verticale par rapport à l'axe longitudinal, et la partie fémorale est en outre courbée autour d'un troisième axe, qui s'étend de manière essentiellement perpendiculaire à l'axe longitudinal ainsi qu'au deuxième axe. L'invention concerne en outre une prothèse de hanche avec une partie fémorale. Selon l'invention, au moins un élargissement (30, 31) est disposé au niveau de la zone courbée autour du deuxième axe (15) et à courbure convexe.
PCT/EP2011/052832 2010-02-25 2011-02-25 Partie fémorale d'une prothèse de hanche, ainsi que prothèse de hanche WO2011104353A1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
DE102010002322A DE102010002322B4 (de) 2010-02-25 2010-02-25 Oberschenkelteil einer Hüftgelenkprothese sowie Hüftgelenkprothese
DE102010002322.1 2010-02-25

Publications (1)

Publication Number Publication Date
WO2011104353A1 true WO2011104353A1 (fr) 2011-09-01

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PCT/EP2011/052832 WO2011104353A1 (fr) 2010-02-25 2011-02-25 Partie fémorale d'une prothèse de hanche, ainsi que prothèse de hanche

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DE (1) DE102010002322B4 (fr)
WO (1) WO2011104353A1 (fr)

Citations (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3067740A (en) 1959-09-08 1962-12-11 Edward J Haboush Hip joint prosthesis
DE2537807A1 (de) * 1974-08-29 1976-03-18 John Charnley Oberschenkelprothese
FR2676914A1 (fr) * 1991-05-28 1992-12-04 Tec Implant Sarl Prothese femorale anatomique.
DE3425002C2 (de) 1983-07-08 1994-06-23 Zimmer Ltd Implantierbare Prothese
DE4437479A1 (de) * 1994-10-20 1996-05-02 Volker Prof Dr Echtermeyer Endoprothese zur Einbringung in den Körper zum Ersatz eines Gelenks, insbesondere eines Hüft- oder Kniegelenks
DE10036636A1 (de) * 1999-07-27 2001-03-15 Saint Paul Bernd Endoprothese für ein Hüftgelenk
EP1958596A1 (fr) * 2007-02-14 2008-08-20 Biomet Merck France Tige fémorale pour prothèse de hanche
US7494509B1 (en) * 2002-02-04 2009-02-24 Biomet Manufacturing Corp. Method and apparatus for providing a short-stemmed hip prosthesis

Family Cites Families (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE19547638C2 (de) * 1995-12-20 1998-05-14 Zimmer Ltd Oberschenkelteil einer Hüftgelenkendoprothese
EP0962199A1 (fr) * 1998-06-04 1999-12-08 Sulzer Orthopädie AG Prothèse de tige

Patent Citations (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3067740A (en) 1959-09-08 1962-12-11 Edward J Haboush Hip joint prosthesis
DE2537807A1 (de) * 1974-08-29 1976-03-18 John Charnley Oberschenkelprothese
DE2537807C3 (de) 1974-08-29 1987-01-22 Charnley Surgical Inventions Ltd., Knutsford, Cheshire Oberschenkelteil einer Hüftgelenkendoprothese
DE3425002C2 (de) 1983-07-08 1994-06-23 Zimmer Ltd Implantierbare Prothese
FR2676914A1 (fr) * 1991-05-28 1992-12-04 Tec Implant Sarl Prothese femorale anatomique.
DE4437479A1 (de) * 1994-10-20 1996-05-02 Volker Prof Dr Echtermeyer Endoprothese zur Einbringung in den Körper zum Ersatz eines Gelenks, insbesondere eines Hüft- oder Kniegelenks
DE10036636A1 (de) * 1999-07-27 2001-03-15 Saint Paul Bernd Endoprothese für ein Hüftgelenk
US7494509B1 (en) * 2002-02-04 2009-02-24 Biomet Manufacturing Corp. Method and apparatus for providing a short-stemmed hip prosthesis
EP1958596A1 (fr) * 2007-02-14 2008-08-20 Biomet Merck France Tige fémorale pour prothèse de hanche

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DE102010002322A1 (de) 2011-08-25
DE102010002322B4 (de) 2013-03-07

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