CA1249195A

CA1249195A - Method and device for fixing a joint prosthesis

Info

Publication number: CA1249195A
Application number: CA000465737A
Authority: CA
Inventors: Ingrid Bruce; Lars Bruce
Original assignee: Idea AB
Current assignee: Lanka Ltd
Priority date: 1983-08-12
Filing date: 1984-10-18
Publication date: 1989-01-24
Also published as: SE8304387L; EP0197920A1; DK171104B1; SE459844B; DK261486D0; WO1986002260A1; US4904267A; DK261486A; SE8304387D0

Abstract

CANADIAN PATENT APPLICATION

OF

INGRID BRUCE and LARS BRUCE

FOR

METHOD AND DEVICE FOR FIXING A JOINT PROSTHESIS

Abstract of the Disclosure:

The invention comprises a method and a device for fixing a joint prosthesis in which all surfaces intended for tissue contact consist of titanium or a titanium-based tissue-compatible metallic material.
For safely anchoring the prosthesis in relation to the bone tissue, use is made of pointed fixing elements which from the side of the bone tissue that should be facing the prosthesis are driven into the bone tissue with their pointed portions, and which are anchored in cement between the prosthesis and the bone tissue or directly to the prosthesis, such that a solid connection 15 established by the bone tissue growing onto the anchored pointed portions. For proper adjustment of the prosthetic joint cup and the prosthe-tic joint ball, these members are moulded under pressure and heat, each respective articular surface being shaped against a model mould of the mating articular surface, and are hardebed or sintered in shape contact for minimizing any aftertreatment.

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Description

1~9195 The present invention relates to a device for promoting the connection and fixing of joint prostheses, in particular hip joint prostheses but also shoulder, knee, foot and finger joint prostheses etc.
The implantation of joint prostheses i5 today general routine within orthopedic surgery. The sur-gical technique generally races surmoun-table difficul-ties. However, a serious problem, apart from infections and thrombosis, is that one or both of the prosthetic components may loosen. The most typical joint recon-struction is the so-called h~p joint reconstruction.
About 5,500 operations of this type were performed in Sweden in 1981 and the commonest reasons therefor is arthosis in the hip joint or joint injuries caused by bone fractures and malformations resulting from other causes, e.g. rheumatic affections.
The problems involved in hip joint reconstruction have been subjected to intensive studies over the last ;, decades and were discussed, for example at the so-called ~ Consensus conference in Stockholm on May 12-14, 1982.
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In a Consensus statement made by the Medical Research Council after the conferencet it was recommended in hip joint arthroplasty~to use a femoral part of metal . ~ :
~ and pelvic part of plastic/ and in routine cases to ; use cement for fixing the prosthesis.
From other sources it appears that by "cement"
i~s generally understood a polymer which is allowed to polymerize in situ. ~he polymerization temperature may vary according to the components used but often con-

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siderably exceeds 47C which is a limit for the tempe-rature to wh ch bone tissue can be exposed without any commencing injury to the tissue resulting in so-called membrane formation.
Many researchers (Rik Huiskis at the Orthopedic ~ , Institute of the University of Nijmegen, E. Morscher at the Institute of Orthopedic Surgery at the Univer-sity of Basel and others) are of the opinion that the material for the femoral paxt of the prosthesis should be selected among stainless steel, cobalt-chromium alloys and titanium, and that plastic should be selected for the pelvic part of the prosthesis. This combination is advantageous in that it entails relatively low friction and is wear-resistant. The choice of material is dictated not only by the mechanical properties of the material but also by the requirement that the material should be biocompatible ~ith the body tissues.
The use of stainless steel has declined to an increasing extent, the major interest being today directed toward titanium, titanium alloys and cobalt-chromium alloys.
Of the metals hitherto tested, titanium seems to be the most tissue-compatible and corrosion resistant, :
and it has the excellent property of being highly resistant to fatigue and (or but) is relatively flexible.
As material for the acetabular cup, researchers primarily reco~mmend polyethylene, Delrin and methyl methacrylate. Hlgh-density polyethylene is extensively used for acetabular cups because of its e~cellent frictional and wear resistant properties in combination

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-- ~24~1~5 with the above-mentioned metals and in that fragments resulting from wear cause a minimum of irritation '' ~IM) to the tissue. Delrin, which has lately come into use, is harder than polyethylene and would scarceIy offer any advantages,over polyethylene. Among other possible materials, mention may be made of ceramic materials with high tissue compatibility. Such materials resist corrosion but are considered unreliable in respect of mechanical properties and may caus~ irri-tation and infec~ions by fragments loosening from the surfaces of the ceramic material.
For fixing the parts of the prosthesis, and in particular the prosthetic part in the femur, use is made of cement which serves to fill the entire space between the prosthesis and the inner side of the bone wall and to distribute the load over as large an area of the bone as possible. Cement materials hitherto used ~plastic glues) ensure good adherence to metal but are inapt to establish a chemical bonding to bone tissue. The main function of the cement therefore is to form a stabilizing filling between the prosthesis and the bone.
~ Although the prosthetic materials for the acetabular .~ .
cup and the femoral head with the stem have been thorough--ly ~ested and give satisfactory results in respect of the friction produced between the prosthetic cup ~ and the prosthetic head or ball, and although materials with suitable elastic properties may be selected, one serious problem remains, i.e. that micromovements ~, . . .

~4~95 occur between the wall of the femoral medullary canal and the stem of the femoral prosthetic part fixed therein because of the loads on the femoral joint head caused by the weight and the movement of ~he body and because the stem~ is not sufficiently skably fixed with respect to the bone tissue in the wall of the medullary canal. Such micromovements which will be most pronounced between the upper and lower ends of the stem too often result in that the stem loosens, thus necessitating reoperation.
The ob~ect of the present invention is to provide a system and a method which ensure safe and permanent anchorage of prosthetic parts of the above~indicated materials having good tissue-compatible and mechanical properties versus bone tissue without adding any undesirable properties.
A further object of the invention is to provide a simplified method for economic production of joint cup and joint head prostheses with perfectly mating articular surfaces of low friction and suitable elastic properties with respect to each other.
According to the invention, these objects have now been achieved by a device and a method having the features stated in the accompanying claims.
The invention will be described in greater detail hereinbelow with reference to the accompanying drawing which shows an acetabular cup prosthesis which is designed in accordance with the invention and fixed to the pelvis by fixing means and by a method for fixing :

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prostheses according to the invention, and which, in longitudinal section, shows part of the ~emur with a prosthesis fixed in the femoral medullary canal and comprising a joink head or ball with a stem conformed to the acetabular cup of the joint.
The acetabular cup prosthesis shown in the drawing consists of a cup-shaped main portion 1 and a layer 2 applied to the concave side of the cup and forming the articular surface of the acetabular prosthesis. The main portion 1 of the acetabular prosthesis i5 preferably obtained by compression moulding a metal powder and sintering the metal powder according to known powder moulding, compression moulding and sintering methods, such that its concave side is provided with pores.
However, it may also be possible to obtain the portion 1 from metal by a suitable cutting technique or a conventional metal shaping technique, such that the concave side is given an uneven structure corresponding to the above-mentioned pores and ensuring ~ood adherence .
to the layer 2 when prepared as described below. A
suitable material for the acetabular portion 1 is selected from any of the metals mentioned by way of introduction, preferably titanium which is known for its tissue compatibility, a tissue~compatible titanium alloy or optionally a cobalt-chromium alloy or any other ; tissue-compatible metallic material.
;~ The cup portion 1 is preferably designed in such a manner that its convex upper face intended to engage the ~j~ 6 9~

pelvis B is also porous or rough to increase the ability of ongrowth of the bone tissue to said surface.
The acetabular portion 1 can be fixed to the pelvis, for instance by means of pins or screws in a manner which is known in conjunction with the fixing o cup prostheses of plastic, hut the cup portion 1 is preferably fixed in accordance with the invention in such a manner that a plurality of pins 3 projecting from the convex side of the portion 1 and consisting of a tissue-compatible metal onto which living bone tissue can grow, are fixed in the material. These pins should have barbs and pointed ends, such that they can be driven into the underlying pelvic bone and mechanically hook onto the bone tissue so as to form a bond which will be subsequently strengthened by the bone growing onto the pins.
Before the acetabular portion 1 is connected to the pelvic bone, the layer 2 is preferably applied according to the invention in such a manner that the cup portion 1 is placed in an injection moulding tool by means of which the layer 2 is injection moulded against a model of the joint ball so as to obtain a good calibration of the articular surface of the joint cup with respect to a joint ball with ~hich it is to cooperate. A suitable material for the layer 2 is preferably selected among any of the initially mentioned plastics or any other tissue-compatible plastic with suitable elasticity and thickness for distributing the loads which generally occur in a hip joint. Suitable plastics are for example plastics of , . '' ~2~ 5 the types polyethylene, Delrin and methyl methacrylate.
Instead of plastic, it is possible to choose a suitable enamel or a ceramic material.
The femoral prosthetic part 5 is preferably prepared in the same way and from the same types of material as the acetabular prosthetic portion 1. By preparing the prosthetic part 5 by moulding, compressing and sintexing a metal powder of a suitable particle size, it is possible to obtain an approximately porous or rough surface to be connected to cement of the type which is generally used for fixing prosthetic stems in the medullary canal of a bone. However, the famoral prosthetic part may also be produced in a conventional way. In this case, too, the surface of the stem portion should be sufficiently porous or rough for adequate ~- adherence to the cement material selected for applylng in `` the medullary canal of the bone.
When the prosthetic part 5 has been prepared, it is inserted in an injection moulding ~ool by m0ans of which there is applied to the joint ball 6 a layer 7 of material which gives a u~iform, smooth articular surface similar to the articular surface of the acetabular prosthesis 1,2. The injection-moulded ma~erial on the joint ball is selected with regard to the injection-moulded material on the ~oint cup or soaket so as to obtain t~e best possible combination in respect of both friction and elasticity between the joint socket and the joint ball, for instance plastic to plastic, enamel to ~, ~ 8 ,, .~ ,, .g5 plastic or ceramic to plastic. ~y injection moulding the layer 7 on a model of the joint socket and vice versa, it is possible to obtain a very accurate fit between socket and ball. By this moulding technique for both the joint ball and the joint socket, the very expensive finishing and polishing operations hitherto used may be reduced or entirely dispensed with.
However, for the combination of arkicular surfaces of the type metal to plastic it is also possible to apply a metallic surface to the joint ball by metal evaporation in vacuum or, possibly, by electrolytic or electrochemical metal deposition. However, these methods generally necessitate the use of more precise manufacturing methods for the joint ball surface to which the Layer 7 should be applied, because it is more difficult to achieve the required exact calibration o~
shapes and dimensio~s by plating or metal deposition than by injection moulding of an in~ection mouldable material. It should be emphasiæed that a substantial advantage of the manufacturing method according to the invention is that it makes it possible to reduce the demand for accuracy in ~he manufacture of the prosthe~ic parts on which the articular surfaces are to be designed by applying a layer of material.
As appears from the above, the acetabular cup prosthesis is fixed to the pelvic bone without the use of cement. For fixing the stem 8 of the prosthetic part 5 in the femoral medullary canal r use is however , .

' -9~5 made of the well-tried technique of embedding the stem in cement 9 filling the entire space between the stem 8 and the wall 10 of the bone. As appears from the introduction to the specification, this method does however not give a fully satisfactory result because the cement may loosen from the bone tissue.
Therefore, the application of cement is supplemented according to the invention by fixing the cement material to the bone tissue by means of elements of a metallic material which is tissue compatible and allows the bone tissue to grow onto the elements and which is "cement-compatible", such that the conventional cement ., .
material used will adhere to the elements.
In accordance with the invention, the metallic fixing elements used are preferably barbed pins 11 si-milar to the pins 3 which are used for fixing the joint cup to the pelvic bone. The barbed pins 11 can be appli-ed to the bone tissue, for instance by driving them into the bone tissue from the inner side of the medul-lary canal by means of a driving tool or by pressing them into the bone tissue by means of any suitable tool.
The pins are fixed in place before the stem of the femoral prosthetic part is inserted and cemented in the medullary canal of the bone. The pins should only pe-netrate into the bone tissue and should of course not project from the outer side of the wall o the bone.
On the other hand, the pins should have, at the inner side of the medullary canal, sufficiently large contact surfaces, contact heads or projections to ofEer an ~ '''' .~
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9s adequate attachment surface for the cement material.
Instead of barbed pins, which are preferred, use may be made of metal screws which may optionally be screwed from the outside so as to extend into the medullary canal of the bone to be enclosed therein and bonded to the cement material.
As an alternative of more or less sophisticated pins, use may be made of metal plates or strips which are provided with pins and to which the cement material to be used for cementing the prosthetic stem adheres.
It may be advantageous to use pins, screws or :``
the like having porous surfaces for good adherence to the cement material and for stable ongrowth of the bone tissue to the pins, screws etc.
It is advantageous to design the metal elements 11 in such a manner that the cement material 9 not only adheres to the metal elements but also will be firmly connected, because of the shape of such elements, by embedding portions thereof. A sufficient number of relatively small pins, screws etc. should be used, especially in the region of the lower end and neck portion of the prosthetic stem, such that there will be a sufflcient number of fixing points to efficiently secure the cement to the wall of the bone.
By using a certain concentration of pins, nails etc. in annular areas in the upper portion of the medullary canal of the bone adjacent the joint ball and at the lower end of the prosthetic stem, it is possible in these areas to obtain concentrated anchorage, .

~2'~ 5 and the use of a centering ring of metal which, accord-ing to conventional methods, is often mounted on the stem, especially at the lower end thereof, may be dispensed with.
The number of such fixing points should however be selected also in consideration of the risk that a reoperation may become necessary despite the reliable fixing. In a reoperation, the fixing points must of course be loosened to make it possible to remove the prosthesis, which speaks for as few fixing points as possible. For loosening the pins in connection with a reoperation, it may become necessary, from the outside, to bore or otherwise break loose the attachments. The loosening of the fixing points will of course become easier, the fewer the fixing points are. If the pins are bored loose, the holes which are left open will be so small that they will be fully healed by growth of bone tissue after a reoperation.
As already intimated above, use is of~en made of a guide or centering means at the outer (lower) end of the stem of the femoral prosthesis to maintain the stem in as correct a position as possible during the cementing operation. In a per se known embodiment, the centering means conslsts of a band-shaped ring disposed on the stem adjacent its lower end and being of the same material as the stem. The ring generally carries a sparse corona of obliquely outwardly-upwardly directed resilient tongues or tines of the same material which are urged by the wall of the bone inwardly towards ~Z~ 5 the prosthetic stem during the insertion thereof in the medullary canal. The ring with its resilient tongues or tines are capable but to an insignifi.cant extent to prevent the loads on the femoral prosthesis from initiating a vibratory and oscillatory movement of the stem in the medullary canal. Such an oscillatory movement, which may initially be microscopically small and has its amplitude at the lower end of the stem, tends to increase with time and may in a relatively short time have a devastating consequence for the retention of the femoral prosthesis.
To pursue the idea of stabilizing the prosthesis in the.femoral medullary canal, it is therefore sug-gested according to the invention that a guide or centering means, at leas~ at the lower end of the prosthetic stem, is fixed by means of hooks, pins ~ .or the like which penetrate the wall of the bone and .:~ consist of titanium or a titanium-based tissue-compatible : material allowing the bone tissue to grow onto the - pins or the like.
~:~ There are many different ways for achieving such a penetration of pins or like elements for ongrowth of bone tissue, which are fixed or being fixed to a guide or centering means of the above type or simply to the prosthetic stem itself.
~ . One way is implanting pins from the outside in ;: the wall of the bone and fixing the pins to the stem.
~;~ Another way is fixing a ring by means of pins or a circle o pins in the bone priox to the insertion . 13 9~95 of the prosthesis) such that the prosthetic stem can thereafter be inserted in the ring or circle of pins with adequate fit therein for stable retention with or without the use of cement. Another possible way according to the invention, which seems promising but has not yet been clinically verified, is using a pin-equipped, expandable annular member 12 which is expandable from the outside and, for example, is of the schematic design intimated in the drawing.
The illustrated annular member 12 is expandable by means of a bolt 13 which with a threaded end por-tion 13' engages in two internally threaded expansion washers 14 on either side of an expandable annular to-rus lS which is mounted at the end portion of the stem 8 and from which a number of pins project radially outwardly, so that they can be urged into the femoral wall 10 by rotation of the bolt 13. The bolt extends through a channel bored ln the stem 8 to a point at the upper end portion of the stem that is spaced apart and : ,~
laterally offset from the joint ball 6. At its upper end, the bolt 13 has a member 17 with which a tool (not shown) can engage.
For moving the expansion washers 14 towards each other for expanding the member 15, one washer has a left-hand thread and the other a right-hand thread, and the thread of the bolt consists of one left-hand threaded portion and one right-hand threaded portion, i.e. the washers 14 and the bolt 13 act as a turnbuckle device in the illustrated example.

~91~5 Instead of the expansion assembly 12 shown in the drawing, it is possible to use any other per se known expandable device suitable for the contemplated purpose, provided it can properly stabilize the stem 8 in the above-described manner by expanding, such that the pins will penetrate into the femoral wall, and/or by expandlng into engagement with and abutment against the inner side of the wall.
The toroid member 15 should consist of a tissue-compatible material, such as titanium or a titanium-based material or a tissue-compatible plastic. It is possible by a suitable choice of material and design to achieve a certain elasticity to force the expandable member 12 (15) to conform to the shape of the medullary canal without neglecting the need for eliminating vibrations or at least reducing them in the prosthetic stem in the femoral medullary canal.
It should be noted in particular that the expandable annular member and the prosthetic stem can be so arranged that the stem can be inserted in the annular member after expansion thereof in the medullary canal before the prosthesis is inserted in place. In this case, the prosthetic stem need not have~a bore and the bolt 13 may be dispensed with, but there will instead be required a tool which can be inserted through the bone or at the end of the medullary canal for expanding said member.
It should be noted that the invention is only schematically illustrated n the drawinq, in which ,.

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for instance the thickness of the cement layer 9 and of the layers 2 and 7 forming articular surfaces is chosen rather Eor purposes of illustration, which also applies to the pins serving as fixing elements.
The thickness of the di~ferent layers and in particular the geometrical shapes of the fixing elements may vary and several modifications of the shape of the fixing elements are possible within khe scope of the invention. Also, it is possible to use many combinations of materials for the fixing elements.
Thus, it is possible, for instance, to make the fixing-elements of steel or any other inexpensive material and to coat the surface with a more biocompatible material, primarily pure titanium or a titanium-based material whlch is particularly tissue-compatible and in other respects biologically acceptable.
It should however be emphasized that the femoral prosthesis need not consist of titanium in its entirety.
~n the contrary, an~embodiment is preferred which consists of a core of for instance steel coated with a titanium metal. The different fixing elements of metal pre~erably consist of for instance steel with a titanium coating in accordance with the above. Fur-ther, it should be noted that the joint prosthesis of the invention can also be used for joints other than hip joints, for instance knee joints, shoulder joints etc., and that it is possible, as a supplement to the illustrated fixing elements, to use metal screws ; 16 ,~ , .
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coated with a surface layer of titanium~ Steel screws with a titanium layer provide -the same tissue compati-bility as titanium screws but are less expensive and, moreover, a suitable elasticity is more readily obtain-able by a combination of steel/titanium surface layers.
Incidentially, such screws may also be used for fixing bone shafts in cases of complicatecl fractures or for strengthening the bone shaft w~ere a joint prosthesis is applied~
Nor is the invention restricted to the method described above where the metallic fixing elements are applied before the prosthetic stem 8 is cemented in the medullary canal. In fact, it is possible, from the outside, to drive or screw fixing elements through the wa11 of the bone and into the cement material:
In order to obviate any impermisslble stresses, use should then be made of fixing elements provided with througnholes allowing cement subjected to pressure to escape therethrough. This method of application can also be carried out after cementing but before the cement has set.
As a supplement to or in replacement o~ the above-mentioned bridging elements in the form of pins, staples, screws or the like between bone cement for fixing a prosthesis with respect to a bone tissue, and the bone tissue itself, the following means are suggested which for the sake of simplicity will be described in connection with a hip joint prosthesis with a stem to be connected to the femoral wall, but may also apply to many othe~ cases where a prosthesis should be fixed to bone tissue, possibly also artificial roots or stems of teeth.
In the open medullary canal of the bone, titanium particles are inserted which are caused to adhere temporarily or more permanently to the bone tissue.
The particle layer may be concentrated or relatively sparse depending on the field of use and on how concen-trated points of attachment are desired. These particles or grains may be applied in any suitable manner, for instance advantageously by spraying through a nozzle.
The particle size may in principle be selected within the range of from ~m to several mm depending on the size of the prosthesis and the thickness of the bone cement layer. Thus, the titanium particles may also be in the form of a very fine power. This powder can be applied by means of fine nozzles before or after appli-cation of the prosthesis but before the application of the bone cement. However, it is ~uite possible and, in some cases, even advisable to mix the tltanium powder or grains with the bone cement.
In tests~on living animal bone tissues, it has been found that the bone tissue grows onto the grains fixed by means of the bone cement, whereby the cement which readily adheres to the prosthesis, as when pins etc. are used, will form a solid bridge between the bone tissue and the prosthesis.
The titanium grain or powder material can be applied in the form of a more or less easy flowing ~ ..

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4~ 5 paste or thin slurry or, if a fine grained titanium powder is used, as a pigment-like substance.
Good results are also anticipated for a method according to the invention in which titanium grains are introduced as a layer between the prosthesis and the bone tissue, whereupon a binder for fixing the prosthesis and for fixing the grains is injected in the powder layer by means of a~ injection needle or in any other suitable way and in such an easy flowing state that the binder will fill the voids between the grains by capillary action.
In the case described above, animal tests have confirmed or given to expect very favourable results which should also apply to human application.
In combination with the fixing and consolidating methods described above, in which use is made of a binder of some kind or also simply bonding by sinter-ing, it may also be possible to use fibres, such as titanium fibres, but also other fibres, such as carbon fibres, are conceivahle.

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Claims

The embodiments of the invention in which an exclusive property or privilege is claimed are defined as follows:

1. A device for fixing a joint prosthesis which has a portion consisting of a body with a spherical articular surface and a portion to be fixed in relation to or at bone tissue, and bridging elements or element for fixing the prosthesis in relation to the bone tissue, said element or elements being made from a material and surface structure allowing the bone tissue to grow onto the respective elements or element, the part of the surface of the prosthesis adapted to face and to become fixed to the bone tissue, having a porous or rough surface of titanium which completely covers and is inseparably connected to the body, said bridging elements having means comprising pointed portions, edges or corners for engaging that side of the bone tissue which, after implantation of the prosthesis, faces said prosthetic surface, such that the bone tissue is allowed to grow onto the elements, said device further comprising anchoring portions for direct and/or indirect anchorage of the prosthesis to the respective bone, by embedding the anchoring portions and bonding same in a cement layer between the prosthesis and the bone tissue.

2. Device as claimed in claim 1, wherein at least some of the bridging elements for engaging the bone tissue have one or more pointed portions or a pointed projection for penetrating into the bone tissue from the side of the bone tissue facing the prosthesis.

3. Device as claimed in claim 1, wherein at least some of the bridging elements has one or more pointed portions or a pointed projection for penetrating into the bone tissue from the side of the bone tissue facing the prosthesis, and one or more barbs for retaining the pointed portion or portions in the bone tissue.

4. Device as claimed in claim 2 or 3, wherein said at least some bridging elements have a base or end portion with means to be embedded in a cement layer between the prosthesis and the bone tissue.

5. Device as claimed in claim 1, wherein the prosthetic body is produced by sintering metal powder and said surface of the body is produced by sintering titanium powder or a titanium-based sinterable metallic powder, such that said surface, at least locally, has a granular and preferably coarse-grained structure.

6. Device as claimed in claim 5, wherein the prosthetic body and said surface are produced by sintering in one and the same sintering process.

7. Device as claimed in claim 6, wherein said surface is produced by a powder of a particle size exceeding that of the powder from which the rest of the prosthetic body is made.

8. Device as claimed in any of claims 1, 2 or 3, wherein the prosthetic body and said surface are produced by sintering a powder based on different metals.

9. Device as claimed in claim 1, wherein the prosthetic body is produced by sintering a steel-based powder and the surface by sinking a titanium-based metal powder.

10. Device as claimed in any one of claims 1, 2 or 3, wherein the bridging elements comprise a corona of bridging elements extending around at least an annular portion of a stem portion of the joint prosthesis to be fixed in the medullary canal of a bone.

11. Device as claimed in any one of claims 1, 2 or 3, wherein the bridging elements comprise a corona of bridging elements extending around at least an annular portion of a stem portion of the joint prosthesis to be fixed in the medullary canal of a bone, the corona of bridging elements comprises an annular expandable member having a plurality of pin-like bridging elements which project from the expandable member and are provided with said surface of titanium or titanium-based material and have pointed portions outwardly directed from said member and are of such a length that said pointed portions are pressed into the wall of the bone upon expansion of the annular member.

12. Device as claimed in any one of claims 1, 2 or 3, wherein the bridging elements comprise a corona of bridging elements extending around at least an annular portion of a stem portion of the joint prosthesis to be fixed in the medullary canal of a bone, the corona of bridging elements comprising an annular expandable member having a plurality of pin-like bridging elements which project from the expandable member and are provided with said surface of titanium or titanium-based material and have pointed portions outwardly directed from said member and are of such a length that said pointed portions are pressed into the wall of the bone upon expansion of the annular member, said expandable member being provided with means for fixing the member by expansion in place within the bone prior to the insertion of the prosthetic stem and being so adapted as to allow insertion of the prosthetic stem in the expandable member after expansion thereof.

13. Device as claimed in any one of claims 1, 2 or 3, wherein the bridging elements comprise a corona of bridging elements extending around at least an annular portion of a stem portion of the joint prosthesis to be fixed in the medullary canal of a bone, the corona of bridging elements comprises an annular expandable member having a plurality of pin-like bridging elements which project from the expandable member and are provided with said surface of titanium or titanium-based material and have pointed portions outwardly directed from said member and are of such a length that said pointed portions are pressed into the wall of the bone upon expansion of the annular member, said device further comprising an expansion device by means of which the expandable member, after it has been applied to the prosthetic stem and the prosthetic stem has been inserted in the medullary canal of said bone, is expandable in a per se known manner from the outer side or outer end of said bone through a channel in the prosthetic stem and/or in said bone.

14. Device as claimed in any of claims 1, 2 or 3, wherein the prosthetic body is in the form of a base which, at one side, supports a joint cup fixed to the base and, at the opposite side, is provided with said surface of tissue-compatible metallic material and carries a plurality of said bridging elements.

15. Device as claimed in any of claims 1, 2 or 3, wherein the prosthetic body is in the form of a base which, at one side, supports a joint cup fixed to the base and, at the opposite side, is provided with said surface of tissue-compatible metallic material and carries a plurality of said bridging elements, the side of the base facing said joint cup having a coarse-grained and/or porous structure and forming a backing surface to which the joint cup, preferably consisting of tissue-compatible plastic, is fixed by infiltrating and bonding the material of the joint cup into the structure of said backing surface.

16. Device as claimed in any of claims 1, 2 or 3, wherein the prosthetic body is in the form of a base which, at one side, supports a joint cup fixed to the base and, at the opposite side, is provided with said surface of tissue-compatible metallic material and carries a plurality of said bridging elements, the joint cup being obtained by injection moulding or compression moulding said material against the base and against a model of a joint ball for calibrating the joint cup surface with respect to the surface of the joint ball prosthesis with which the joint cup is to cooperate, such that any aftertreatment of the joint cup surface is limited or made superfluous.

17. Device as claimed in claim 5, wherein the bridging elements consist of titanium powder or titanium grains having edges, corners or other structure for partial penetration into the bone tissue or for intimately contacting the bone tissue, such that the bone tissue is allowed to rapidly grow onto said grains, while the sides of the grains facing away from the bone tissue are exposed to be connected by means of a binder between the prosthesis and the bone tissue.

18. Device as claimed in claim 17, wherein the titanium grains have a size ranging from um to several mm.

19. Device as claimed in claim 17, wherein the titanium powder is applied as a fine powder, which is preferably self-adhesive by its small particle size.

20. Device as claimed in claim 17, wherein the titanium powder or titanium grains form a filler in bone cement for fixing the prosthesis to the bone tissue.

21. Device as claimed in any of claims 1, 2 or 3, wherein, for strengthening the bridging elements or the prosthetic material, use is made of fibres of titanium or fibres of any other tissue-compatible material, such as carbon fibres.

22. Device as claimed in any of claims 1, 2 or 3, wherein use is made of titanium fibres and/or carbon fibres as bridging elements or as a supplement to bridging elements.

23. A method of producing a joint ball prosthesis consisting of a joint ball with a stem to be inserted and fixed in the medullary canal of a bone, wherein the ball and the stem are produced by moulding and sintering a powder of a tissue-compatible metallic material, preferably titanium or a titanium-based metallic material, said stem being provided with a coarse-grained, porous and/or rough surface structure, and the surface layer of said joint ball being made from a fine-grained powder of said material integrally with the rest of the ball by moulding and sintering, such that the need for calibrating aftertreatment of the joint cup surface is minimized.