SURGICAL BIOCOMPOSITE MATERIAL AND A METHOD FOR PRODUCING THE MATERIAL

Abstract: Biocomposite material for bone surgical applications comprises at least one bioceramic piece (1) (bioceramic component) and at least one material component (2) which has been manufactured of at least one polymer or corresponding, which material component (2) has at least one common boundary surface with the bioceramic component. The material component (2) comprises at least reinforcement elements which have been manufactured of essentially resorbable material like polymer, copolymer, polymer mixture and/or ceramic material. The material component (2) can include binding material which is manufactured essentially of resorbable polymer, copolymer or polymer mixture. The material component (2) contains at least in tissue conditions open porosity.

Description: Surgical biocomposite material and a method for producing the material This invention describes a biocomposite material, which has been defined more accurately in the introduction part of Claim 1. It has been found that many ceramic materials have pro- perties, which allow their use as bone graft materials. Ceramic materials (bioceramics) , which are tissue compa¬ tible and/or which form chemical bonds with bone tissue and/or which promote the growth of bone tissue, are e.g. calciumphosphate: apatites like hydroxyapatite, HA, Ca. Q (PO 6 (OH) - (R.E. Luedemann et al. , Second World Congress on Biomaterials (SWCB) , Washington, D.C., 1984, p. 224), trade names like Durapatite, Calcitite, Alveograf and Permagraft; fluoroapatites; tricalciumphosphates (TCP) (e.g. trade name Synthograft) and dicalciumphosphates (DCP magnesiumcalciumphosphates, β-TCMP (A. Ruggeri et al. , Europ. Congr. on Biomaterials (ECB) , Bologna, Italy, 1986, Abstracts, p. 86); mixtures of HA and TCP (E. Gruendel et al. , ECB, Bologna, Italy, 1986, Abstracts, p. 5, p. 32) aluminiumoxide ceramics; bioglasses like SiO j -CaO-Na-O-P ^ O e.g. Bioglass 45S (structure: SiO_ 45 wt-%, CaO 24,5 %, a 2 0 24,5 % and P 2 0 5 6 %) (C.S. Kucheria et al. , SWBC, Washington, D.C., 1984, p. 214) and glass ceramics with apatites, e.g. MgO 4,6 wt-%, CaO 44,9 %, SiO- 34,2 %, P 2 0 5 16,3 % and CaF 0,5 % (T. Kokubo et al. , SWBC, Washing ton, D.C., 1984, p. 351) and calciu carbonate (F. Souyris et al. , EBC, Bologna, Italy, 1986, Abstracts, p. 41) . The applications of the above ceramic materials as synthe¬ tic bone grafts have been studied by different means by using them for example both as porous and dense powder materials and as porous and dense macroscopical samples as bone grafts. Also ceramic powder - polymer composites have been studied in this means (e.g. W. Bonfield et al. SWBC, Washington, D.C., 1984, p. 77). Some bioceramics are resorbable like for example tri- calciumphosphate (see e.g. P.S. Eggli et al. , ECB, Bologna, Italy, 1986, p. 4) and calciumcarbonate (F. Souyris et al. , ibid, p. 41) . The most known of the nonresorbable bioceramics is aluminium oxide. In literature it has been reported that some bioceramics, like hydroxyapatite, are both resorbable (W. Wagner et al. , ECB, Bologna, Italy, 1986, Abstracts, p. 48) and nonresorbable (biostable) (e.g. G. Muratori, ibid, p. 64) . Resorbable. bioceramics dissolve in tissues slowly and/or they are replaced by the minerals of bone tissue. On the other hand, the bio¬ stable bioceramics remain in the tissues in an unchanged state, in such a way that the bone tissue grows into contact with the bioceramic. Porosity of bioceramic is advantageous, because the bone tissue can grow into the open porosity, if the pores have a suitable size. " On the other hand, a problem of macros¬ copic bioceramic samples and especially of porous samples is their brittleness. The brittleness of bioceramics has been tried to compensate by manufacturing of ceramic powders and of biostable or of resorbable polymers compo¬ sites, where the ceramic powder particles have been bound together by means of a polymer. This has been achieved e.g. by pressing the mixture of bioceramic powder and polymer powder by means of heat and pressure into a com¬ posite piece or by binding bioceramic powder by means of a reactive polymer to a composite piece. Such composites are tough when suitable polymers are applied. Composites of a bioceramic powder and resorbable polymer have been describede.g. in a Finnish patent application 863573. The ceramic powder - polymer composites have a disadvan¬ tage that the presence of binding polymeric material prevents the direct contact of bioceramic powder particles and bone tissue to each, other and therefore delays and prevents the growth of the bone tissue on the surface of composite material and inside of it, because the bone tissue does not have such an affinity to grow on the surface of biostable or resorbable organic polymers as it has to grow on the surface of bioceramics or into their internal open porosity. As a consequence the growth of new bone and the healing of tissue proceeds more slowly with bioceramic - polymer composites than with pure bio¬ ceramics (e.g. according to S. Ishida et al. , ECB, Bologna Italy, 1986, Abstracts, p. 86, the growth of new bone on the surface of 70 % hydroxyapatite filler - triethylene- glycoldimethacp late composite occurred in studies done with rabbits 2.-3 times more slowly than the growth of new bone on the . surface of pure sintered hydroxyapatite). Bioceramics like hydroxyapatite are applied generally as bone graft materials in powder form for filling of bone defects or for alveolar ridge reconstruction by injecting the hydroxyapatite powder/water (or blood) mixture (partic size typically 10-50 mesh) on the bony surface of alveolar ridge into a cavity which has been done below the gxngival tissue. The bone tissue grows rapidly into contact directl with hydroxyapatite particles, which when biostable remain as part of the forming new bone or are resorbed and replac later with new bone. The powder-like bone graft materials have, however, a disadvantage that they remain at their place only after the connective tissue and/or growing bone tissue binds them to their place. For example, in the case of hydroxy¬ apatite powders applied for alveolar ridge augmentation this will take about one month. Before the powder particles have been bound to their place by means of tissue growth, the powder can move easily from the place, where it should be, when mechanical forces (e.g. biting) affect upon the soft tissues- which surround the powder particles. This can lead to a deterioration of good operation result or it is n achieved at all or it is achieved only partially. The Finnish patent application 863573 and the corresponding PCT application FI87/00119 describe supporting struc¬ tures which have been manufactured of resorbable polymer or composite and which can be applied to immobilize bio¬ ceramic particles to their place on the surface of bone. The applications of above invention have been- restricted, however, surgically to such operations, where the bio¬ ceramic powder can be located on a certain restricted area which is surrounded by suitable tissues. The resorb¬ able supporting structures of the above invention, like chute-like, box-like, flat tube or bag-like structures cannot be applied e.g. in the reconstructive surgery of flat bones of maxillofacial region or of skull. Additionall the strength of the system comprising e.g. the chute or the corresponding and bioceramic powder is based only on the structure of the chute or the corresponding, when the bioceramic particles are not bound together by primary chemical bounds. It has been found that bone tissue grows as a rule rapidly and without problems into bioceramic pieces which contain suitable open porosity. Because of the brittleness of these materials they can be, however, broken easily during operation or after it before the bone tissue has grown into the pore structure of ceramic material. Also solid dense bioceramics are often brittle especially if they are thin, plate-like or curved pieces. If the plate is broken during operation or soon after it the pieces of the plate can move in tissues and cause problems to the patient. The strength, like compression strength, of porous bio- ceramic pieces can be increased by coating the bioceramic sample with a resorbable or biostable polymer. The poly¬ meric coating gives to the sample, however, only a limited increase of strength, because the strength of polymers is as a rule only moderate and the stiffness (the elastic modulus) is small in comparison to ceramics. Therefore even small mechanical stresses can break easily the bio- ceramic part of composites manufactured of a porous bio¬ ceramic material-and of a polymeric coating, because as a consequence of the small elastic modulus of polymer the external stressed, are shifted already after small deformations to the ceramic component of the material. EP-patent application 171884 describes an endoprosthetic device which comprises polyaryletherketone (PEEK) and possible additional biostable reinforcing fibres, like carbon fibres, where the shifting of fibres into tissues can be prevented by means of a polymer-rich surface layer on the surface of the device. Further the above invention describes devices, which comprise a massive ceramic core component, which has been coated at least partially with tissue compatible biostable polymer. When the above devices are applied surgically the biostable polymers and fibres remain permanently into the tissue-s of the patient and e.g. in the case of the application of ceramic block coated with a biostable polymer the polymer layer separates the ceramic core and the surrounding tissues permanently from each other preventing in this way the advantageous growth of surrounding tissues into direct contact with the ceramic block. In addition biostable polymers and fibres may release into surrounding tissues small particles, fibre fragments, or other debris as a consequence of wear,: breakage or processing (see e.g. EP 171884 p. 14, lines 16-22). Small particles, fragments or debris cause as a rule in the surrounding tissues or in the nearby lymph nodes longlasting, even years lasting, foreign body and inflammation reaction. In this invention we have found unexpectedly that when one manufactures a biocomposite described mainly in the characterization part of Claim 1 , one obtains a structure, which has the advantages of known bioceramics and bio¬ ceramic - polymer composites, but from which the proble- matic properties and weaknesses of the known materials have been mainly eliminated. In the materials of this invention there are combined to each other in a sur¬ prising way the good mechanical properties of the mate¬ rial (like stiffness, toughness, strength and integrity) during operation and after it the desired period of time (at least the time which the safe healing demands) and also the easy and safe handling of specimen during ope¬ ration. The materials of this invention have as surprising advan- tages in comparison to the materials of EP 171884 (a) that the tissues which surround the biocomposite can be begin to grow immediately after the operation to direct contact with bioceramic component or into it through the open porosity of the material component or from the free surfaces of bioceramic component and (b) that after the resorption of material component the tissues which are in contact with the material component can grow also from this part advantageously into contact with bioceramic sample or also into its open porosity. Further for patients is a surprising additional advantage that if biocomposite releases polymeric particles or fibre fragments they cause in the surrounding tissues or in the nearby lymph nodes only temporary reactions, because the cells of living tissues use these resorbable materials in their metabolism e.g. as nutrients» The biomaterials of the invention describe an especially high improvement of mechanical properties in comparison to known bioceramic - polymer composites when the bio¬ ceramic component is coated at least partially by using as a coating agent continuous reinforcement fibre, rein¬ forcement fibre bundle or a thread which has been construc¬ ted of short fibres or corresponding reinforcement struc¬ ture, which may be coated with resorbable polymer and/or is wetted with polymer on the surface of bioceramic component.. This reinforcement fibre, -bundle or thread can be installed on the surface of the bioceramic component e.g. by means of the filament winding method. The filament winding method is applied advantageously in such a way that the bioceramic component and/or the device which feeds the reinforcement fibre rotates at least around one axis and/or moves at least in the direction of one axis. The biocomposites of. this invention manufactured by the above methods are even in case of porous biocerami components so strong and tough (bending strength typicall 2 over 100 N/mm ) that they can be applied in manufacturing of fixation devices of bone fractures (devices like rods, plates, intramedullary nails and so on). This is a sur¬ prising advantage because the known porous ceramics as such or as coated with nonreinforced polymers are too weak and brittle to such applications. When the .surface of the bioceramic component of the biocomposite of this invention is at least partially free of polymeric material an additional surprising advantage is the rapid fixation ' of biocomposite to the living tissues because of the rapid cell growth on the free surface of the bioceramic component and into its possible open porosity. When the open porosity of porous bioceramic component is at least partially free of the polymeric material, a surprising combination of good mechanical strength properties of the material, for patients secure handling of implants, rapid fixation of biocomposite with the living tissues and small loading of living tissues with resorbable foreig body material (resorbable polymer) is obtained. When the biocomposite of the invention is manufactured of resorbable polymer component and of resorbable reinforceme elements one special advantage is that the polymer com¬ ponent and reinforcement elements are resorbed completely after the bioceramic has been reinforced sufficiently as a consequence of the cell growth on the surface of the bioceramic and/or into its open porosity. This invention describes the above biocomposite materials, a method to manufacture them and their application as surgical implants e.g. to fill a defect, hole or corres¬ ponding in a bone, to augment the dimensions of the bone tissues, like in the case of the augmentation of alveolar ridges, to change the form of bone tissue in reconstruc- tive surgery of maxillofacial bones or scull bones or in a corresponding meaning, or in fixation of bone frac¬ tures, osteotomies, arthrodesis or joint damages. The material component of the biocomposites of the inven¬ tion can contain resorbable thermoplastic or reactive thermosetting polymers, copolymers or polymer mixtures. . Resorbablepolymers, copolymers and polymer mixtures are organic high molecular weight materials, which are depoly- merized in tissue conditions by means of physicochemical hydrolysis and/or enzymatic activity. The material which is depoly erized to monomers or oligomers is removed. from the living tissues by means of the normal metabolism of cells e.g. by means of energy production reactions or synthesis of protein molecules in the living cells. An - advantage of surgical products and devices (i pants) which are manufactured of resorbable polymers is the fact that they are removed from the living tissues after they have fullfilled their task without needing a separate removal operation, like the implants which are manufactured of biostable materials (like of metals) often need. Table 1 shows some important nowadays known resorbable polymers which can be applied in the biocomposites of this invention. Table 1. Resorbable polymers which are suitable to biocomposites. Polymer Polyglycolide (PGA) Copolymers of glycolide: Glycolide/L-lactide copolymers (PGA/PLLA) Glycolide/trimethylene carbonate copolymers (PGA/TMC) Polylactides (PLA) Stereocopolymers of PLA: Poly-L-lactide (PLLA) Poly-DL-lactide (PDLLA) L-lactide/DL-lactide copolymers Copolymers of PLA: Lactide/tetramethylglycolide copolymers Lactide/trimethylene carbonate copolymers Lactide/ό-valerolactone copolymers Lactide/ε-caprolactone copolymers Polydepsipeptides PLA/polyethylene oxide copolymers Unsymmetrically 3 , 6-substituted poly-1 ,4-dioxane-2 ,5- diones Poly-β-hydroxybutyrate (PHBA) PHBA/β-hydroxyvalerate copolymers (PHBA/HVA) Poly-β-hydroxypropionate (PHPA) Poly-p-dioxanone (PDS) Poly-δ-valerolactone Poly-ε-caprolactone Methylmethacrylate-N-vinyl pyrrolidone copolymers Polyesteramides Polyesters of oxalic acid Polydihydropyrans Pol alky1-2-cyanoacrylates Polyurethanes (PU) Polyvinylalcohol (PVA) Polypeptides Poly-3-malic acid (PMLA) Poly-S-alkanoic acids Reference: P. Tδrmala, S. Vainionpaa and P. Rokkanen in IVA's Beijer Symposium "Biomaterials and Biocompatibility", Stockholm, Sweden, August 25-26, 1987. In addition to the above polymers there are a lot of other polymers like polymers of natural origin and modified poly¬ mers, which are at least partially resorbable in tissue conditions and which therefore can be applied according to this invention. Such polymers are for example collagen and its derivatives (Catgut), chitine polymers, gelatine (crosslinked gelatine) and cellulose derivatives (e.g. trade name Surgicel) . Several factors contribute to the resoprtion rate of resorb able polymers in physiological conditions. Such factors are e.g. the structure of polymer, the structure and form of the resorbable sample and the biological environment. The resorption rates of the resorbable polymers can vary in different cases from about one week to several years. In the biocomposites of the invention can be applied es¬ pecially well such resorbable polymers, copolymers or poly¬ mer mixtures or structures which are constructed of *them, which retain at least part of their mechanical strength at least some weeks or months and are resorbed during sever months or during a few years. With special caution one " can use also polymers with more rapid resorption rates and on the other hand the use of polymers with more slow resorptio rates does not cause as such disadvantages in surgical use. One can apply in the biocomposites of this invention as a material component e.g. glass-, carbon-, aluminium oxide-, phosphate and other ceramic biostable or resorbable fibres, aramide-, polyester-, polyamide- and other biostable polyme fibres and/or resorbable polymer fibres like e.g. polylacti polyglycolide-, glycolide/lactide-copolymer-, polydioxanone poly-S-hydroxy butyrate-, glycolide/trimethylenecarbonate- or ε-caprolactone fibres or other fibres which have been manufactured of polymers given in Table 1 or e.g. chitine polymer (chitosane) fibres and above mentioned fibres bound together with some resorbable polymer, copolymer or polymer mixture . It is self-evident for experts of this field that to the polymer and/or to the fibres can be mixed different addi¬ tives which facilitate the processing or use of material or which modify the properties of the material. Such addi tives are e.g. colours, stabilizing agents or ceramic powders. The ceramic of the biocomposites of this invention can be porous or nonporous ceramic block, which has been manufac- tured e.g. by sintering of ceramics given on side 1 like of calciumphosphates, fluoroapatites , calciumcarbonates, magnesiumcalciumphosphates, bioglasses, glass ceramics or of mixture of ceramics. Biocomposites of this invention can be manufactured especi ally advantageously of bioceramics which have open poro¬ sity, but also nonporous bioceramics can become more secur for surgical use by combining them with resorbable reinfor ment elements according to this invention. It is advantageous that after the implant has been install by surgical operation that the bioceramic component of bio material and the bone tissue have at least partially direc contact with each other in such a way that no other tis or no other material (like e.g. binding polymer) does form between bioceramic component and bone tissue a completely continuous solid layer. When the bioceramic component and the bone tissue have a direct contact with each other one can obtain rapid, secure and safe filling and healing of a ^ defect or of a hole in the bone or healing of bone reconstructed with biomaterial or healing of frac- ture, osteotomy or arthrodesis which has been fixed with biomaterial. When the above mentioned direct contact between bioceramic component of the implant and bone tissue exists the cells of the new bone can grow directly from the surface of the ' bone tissue rapidly close to the surface the bioceramic (and also into the pores of bioceramic when it includes suitable open porosity; pore size e.g. the order of mangitude 200 μm) . This guarantees the most rapid and best way for binding of bioceramic component and bone to each other and also for reinforcing the bioceramic component by means of cell growth into its pores. When one applies known solid and porous bioceramics as bone surgical implant materials one obtains a good clear contact between bone tissue and bioceramic when a suitable bioceram sample is located directly on the surface of the operated bone or into a hole, defect or corresponding in the bone. A problem of such known bioceramic samples is, however, the above mentioned brittleness, which cannot be eliminated merely by polymer coating. It is possible to achieve also a good direct contact betwee bone " tissue and bioceramic.when one applies bioceramic , powders as bone implants by locating the bioceramic powder on the surface of bone or into a defect, hole etc. in the bone. The disadvantages of powders are, however, the above- mentioned possibility of migration of powder particles and the abscence of macroscopical mechanical properties of the powder. Also the application of a supporting struc¬ ture, which surrounds at least partially the powder, is not suitable to some operations like to reconstruction of flat maxillo-facial bones because the location of thin bio¬ ceramic powder layer (e.g. 1-6 mm layer) below a wide, low supporting structure (like a chute) is a difficult task. One can manufacture thin, plate-like, curved or correspondi samples by binding bioceramic powder with biostable and/or resorbable polymer to a composite. However, the binding of bioceramic powder with biostable and/or resorbable poly¬ mer slackens the growth of new bone and the healing process. Such materials are often also too ductile to such fixations where high stiffness is needed (e.g. in the intramedullary nailing of fractures of long bones) . In using the biocomposites of this invention one can eli¬ minate effectively all the problems of the above-mentione known bioceramics and bioceramic-polymer composites by com bining to each other macroscopical bioceramic samples (1) and essencially resorbable material components (2) which include reinforcement elements. The material " component (2) of these -biocomposites gives to them the toughness, stren and security of handling, because the strong and tough ma¬ terial component supports the brittle bioceramic component as a consequence of the high strength, toughness and high modulus of reinforcement elements. Therefore only very big external stresses can cause deformations in the bioceramic component. On the other hand, the free surface, free surfaces or the parts of free surfaces of the bioceramic component make possible the rapid growth of bone tissue and its fixation to the composite. The resorbable polymer component (2) is resorbed advantageously later away, when its supporting effect is not needed any more because the bone fracture, osteotomy or arthrodesis has been healed and /or the bone tissue has grown close to the ceramic. component (and pos¬ sibly into its open porosity) . If one applies additionally biostable reinforcement fibres, they form after healing into the tissue an inert remnant. The composites of this invention can be used in manufac¬ turing to different surgical operations suitable macros¬ copical samples like plates, cubes, cylinders, tubes, chutes, rods or other samples with corresponding form and geometry. It is possible also to manufacture of these composites samples which have the form of bones or parts of them and which samples can be applied e.g. in reconstructive bone surgery. Figures 1-11 describe some typical embodiments of the biocomposites of this invention. In the biocomposites of Figures 1-11 the bioceramic com¬ ponents (1) have been described as white, dotted regions and the reinforcement containing material components (2) as ruled regions (the ruling describes fibre rein- forcement) . Figure 1a shows as a perspective figure a plate-like biocomposite sample which is formed of a plate-like bio¬ ceramic component (1) and of a polymer component (2) which is reinforced with a fabric which has been con— structed of fibres (L) and which polymer component has been fixed on the surface of the bioceramic component. It is natural that also other reinforcement element struc¬ tures can be applied in this connection like e.g. parallel fibres or fibres which are randomly oriented on the surface of the bioceramic (like felts; non-vowen gauches, short fibres etc.) and film-fibres. The reinforcing can be used -in such a way that the reinforcement elements are located on the surface of the bioceramic component. There¬ after the reinforcement elements can be impregnated with monomer, oligomer, polymer or their mixture by using techniques which are based on heating, pressure, solvents, radiation or to catalytis reactions. The reinforcement elements can be located on the surface of the bioceramic component simultaneously with the polymer component. In every case as a consequence a biocomposite is obtained, to which the fibre reinforcement of the material component (2) gives the unexpectedly high strength. According to an advantageous embodiment the polymer com¬ ponent (2) contains open porosity or holes, through which the tissues above the polymer component can grow rapidly through the polymer component and to contact with the bioceramic component. Such a biocomposite is shown in Figure 1b schematically. In this case the fibre rein¬ forced (L) polymer component (2) contains holes or pores (H) . Open porosity can be manufactured to the polymer com- ponent by applying typical methods which are known in the polymer technology like e.g. by mixing with polymer before manufacturing, powdery soluble additive and by dissolving the additive away from the final biocom- posite. One can apply also foaming agents in the polymer component to get open porosity to it. Into the polymer component containing polymeric binding agents one can make bigger holes e.g. by working mecha¬ nically parts of the polymer component away by drilling or by milling. Holes are also obtained easily on the sur¬ face of material component (2) when part of the surface of bioceramic component (1) is left without coating or part of the surface of the bioceramic component is covered before coating with some kind of protective device and by removing the protective device after the coating of the biocomposite. The material component (.2) of the biocomposite of the invention can be porous or it can contain holes because the -fibre reinforcement gives to the biocomposite good mechanical strength.-pro- perties. This is achieved especially well when the rein¬ forcement elements are continuous surrounding pores or holes. In such cases the reinforcement elements give a good reinforcement effect without preventing the cell growth into the pores or holes. The reinforcement elementphase of the material component (2) of the invention may be manufactured essentially about resorbable material like polymer, copolymer, poly¬ mer mixture and/or ceramic material and the possible binding material of the reinforced material component can be resorbable polymer, copolymer or polymer mixture. This polymer component may include also bioceramic powder which facilitates the growth of cells into the polymer component. Figure 1c shows a plate-like biocomposite of this inven- tion, which has been manufactured by means of the fila- ment winding method. This biocomposite comprises a bioceramic core and a reinforcement fibre layer which has been wound on the surface of the bioceramic core. It is also possible to manufacture by filament winding such biocomposites where the material component (2) is porous when the reinforcement elemen fibres are wound on the surface of the ceramic core in such a way that between the reinforcement fibre bundles are left gaps (see e.g. Figure 8c). Filament winding is an especially advan¬ tageous method to manufacture plate-like bioceramic samples, because such plates have optimal strength and stiffness pro¬ perties and . therefore such biomaterials can be applied in manufacturing of fixation plates for bone surgery. Such biocomposites as are described in Figures la - lc can be applied e.g. in reconstructive bone surgery. Figure 2 shows schematically as a cross-section figure how the biocomposite sample is located on the surface of the bone tissue in such a way that the free lower surface of the bioceramic component (1 is located into contact or close to the surface (3) of the bon which will be reconstructed. This secures the rapid fixation o the biocomposite to the bone as a consequence of the growth of new bone tissue close to the bioceramic. If one applies a bioceramic component which contains open porosity it can be impregnated before operation or during operation with living autogenic cancellous bone which is sludged with blood or tissu fluids and which has been taken from some other bone of the patient (like the iliac crest) . The living osteoblasts or preosteoblasts of such autogenic cancellous bone start refor¬ mation of new bone rapidly also into the open porosity of the bioceramic. It is possible also to impregnate the open porosit of the bioceramic with chemical additives which facilitate the cell-growth and/or with antibiotics to prevent the growth of micro-organisms inside of the bioceramic component. Depending on the form of the bone which shall be reconstructed (e.g. curved bone surfaces) one can manufacture curved or other plate-like composites (e.g. Figure 2b) . The material component (2) gives to the biocomposite strength and toughness and it does not slacken or disturb significantly the growth of the new bone on the biocerami or into its open porosity, because the polymer component according to Figures 1 - 2 is on the other side of the bioceramic component than the bone tissue to which the material is fixed. The biocomposite can be fixed to bone e.g. with metallic or polymeric threads, screws, pins or corresponding. The biocomposite is an especially advantageous material for screw fixation. As a rule a brittle plate-like bioceramic cannot be fixed to bone by screws because it is broken easily during such an operation, but the tough reinforced material component (2) on the surface of the bioceramic component (1) makes possible the fixation of plate-like biocomposite with screws R to bone (3) like is shown schematically in the cross-section Figure 2c. The tough material component (2) gives for a surgeon possibilities to form the biocomposite during the ope¬ ration. As an example the cross-sectional Figure 3 shows how the bioceramic component (1) of biocomposite can be equipped with V-like grooves and how the biocomposite can be bent along these grooves because the tough polymer component can be deformed without breaking it. In this way the straight biocomposite sample can be changed to curved. Such a curved sample can then be fixed on the surface of the bone e.g. by screws. Such plate-like biocomposite samples which are described in Figures 1 - 3 can be stacked to layered samples as is shown schematically in Figure 4. In such stacked struc¬ tures bioceramic components (1) and material components (2) can occur alternately. When one applies porous bio- ceramic components (1) and porous fibre reinforcement material components (2) it is possible to manufacture even big strong, tough bone grafts according to the Figure . When the biocomposite of the invention has been manufac¬ tured of non-porous bioceramic component the boundary surface between the bioceramic component (1) and ma¬ terial component (2) is pronounced when the material component (2) is located on the surface of the bioceramic component (1 ) as is shown schematically in the cross-sectional Figure 5a. When the bioceramic component contains open porosity its boundary surface with the material component is a complicated three-dimensional network if the material component contains a binding polymer because the binding polymer penetrates during the manufacturing process of the biocomposite at least somewhat into the pore structure of the bioceramic. Such a case has been given schematically in the cross-sectio¬ nal Figure 5b. The strength of the boundary surface and therefore also the strength of the whole biocomposite can be controlled by changing the penetration dephth of polymer into the pores of the biocomposite. Figures 6a - 6c show some cubic biocomposite samples of this invention. Figure 6a shows a biocomposite where the material component layers (2) have been fixed on the opposite surfaces of the bioceramic sample (1). Such a material can be used to replace e.g. parts of flat bones. Figure βh shows a biocomposite where the cubic bioceramic piece (1) has been surrounded with a material component (2) in such a way that the upper and lower surfaces of the bioceramic piece are free. Figure 6c shows a bio¬ composite, where the bioceramic piece (1) has been rein¬ forced internally with one or several elongated material components (2) . Figure 7 shows some cylindrical biocomposite samples of this invention. Figure 7a shows a flat, cylindrical bio¬ composite sample, which comprises a bioceramic core (1) and a material component (2) which surrounds like a hoop the bioceramic core. It is advantageous to manufacture the hoop of totally resorbable polymeric material and reinforce it with resorbable fibres. The. biocomposites of Figure 7a can be applied e.g. as arthrodesis implants in operations of joints and vertebrae (see e.g. example 6) Figure 7b shows a cylindrical biocomposite sample, which comprises an outer tube-like bioceramic component (1) and an inner cylindrical material component (2) , which can also be hollow (tube-like) like in the case of Figure 7c. Figure 7d shows a cylindrical biocomposite sample, which has been constructed of bioceramic-(2) and material components which are located within each other. The biocomposites of Figures 7b - 7d can be also applied as arthrodesis implants and also as fixation materials of bone fractures and osteotomies. Figure 8 shows some rod-like and tube-like biocomposites of the invention, which can be applied e.g. in fixation of long-bone fractures, as intramedullary nails and as fixation rods in treatment of cancellous bone fractures, osteotomies and arthrodesis. Figuer 8a shows a non-porous bioceramic rod (1) which has been coated with fibre reinforced polymer (2) . Figure 8a' shows the cross-section of this biocomposite in the plane a-a. The tough, reinforced material component on the surface of the bioceramic rod gives for the rod ex¬ cellent toughness- and strength properties. Figure 8b shows a biocomposite rod', which comprises a bioceramic core (-component (1)) with open porosity and a fibre reinforced polymeric coating (-component (2) ) . Such a biocomposite rod is light, strong, tough and stiff as a consequence of this material combination. Figure 8c shows a tube-like biocomposite sample, which consists of a tube-like bioceramic component (1) which advanta- geously contains open porosity and of a polymer-fibre composite (material component (2) ) which has been wound on the bioceramic component. The winding is made advan¬ tageously in such a manner that between the wound fibre bundles remain openings like in the case of Figure 8c. Polymer-fibre composite can be fixed on the -surface of the bioceramic tube by feeding on the surface of the rotating bioceramic tube a fibre bundle which has been impregnated with a polymer. If one applies a reaction polymer (like e.g. polyurethane) the polymer can be har¬ dened only on the surface of the bioceramic tube, which leads to the fastening of the material component (2) on the surface of the bioceramic tube. If one applies a thermoplastic polymer the fibre bundle can be impregnated before winding with the solution of the polymer and the solvent can be evaporated when the fibre bundle is fas¬ tened on the surface of the bioceramic tube during winding. It is also possible to feed the fibre bundle through the melt of the thermoplastic polymer and to solidify polymer at the same time when the fibre bundle is wound on the surface of the bioceramic tube. Figure 9 shows some basic methods of filament winding (A = angle winding, B = radial winding, C = pole winding, D = weaving winding, E = multiaxial winding and F = circle winding (I. Airasmaa et al. "Lujitemuovitekniikka" (Reinforced plastics technology) , Helsinki, 1984)), which can be applied in manufacturing of the biocomposites of this invention. It is natural that also other filament winding methods than those shown in Figure 9 can be applied in this connection. In manufacturing of biocomposites of this invention it is possible to achieve the highest reinforcement element/ binding polymer ratio when one applies the filament winding methods. The reinforcement elements can be directed optimally by changing the winding directions. Therefore the composites of Figure 8c (like composites of 1c and corresponding materials) have many excellent proper¬ ties. They are strong and tough because of the wound reinforced surface layer. They are light because of the hollow structure and of the porosity of the bioceramic component. The living tissues (bone- and other tissues) can grow rapidly into these biocomposites through the openings between the polymer-fibre bundles and further into the open porosity of the bioceramic tube. Such bio¬ composites can be applied e.g. in intramedullary nailing of long bones. Figure 10 shows a chute-like biocomposite sample, which comprises a chute-like bioceramic component (1) and a reinforced material component (2) which has been laminated on the surface of the bioceramic component. Such bio- .composites can be applied e.g. as replacements of parts of small tube-like bones. Figure 11 shows a mandibular implant manufactured of a biocomposite of the invention. This mandibular implant consists of a bioceramic piece (1) which is of its cross- section a chute (Figure 11a) and of a fibre reinforced material component (2) which is laminated on the outer surface of the bioceramic (1). The space inside of the chute can be filled advantageously e.g. with autogenic cancellous bone, with bioceramic powder (like with apa- tite or with a mixture of bone and bioceramic powder, which facilitates the rapid ossification. In the embodiments of Figures 1 - 11 can be applied non¬ porous or porous, biostable or resorbable bioceramic components and resorbable polymers in a nonporous or porous form, reinforcements like biostable and/or resorb¬ able fibres, film-fibres or other reinforcement elements or structures which have been constructed of them. It is advantageous to apply in fixation of bone fractures, osteotomies, arthrodesis or joint traumas biocomposites, where both bioceramic component and material component have been manufactured of resorbable materials. In such cases the whole biocomposite is resorbed and replaced by a new bone or another living tissues after the fixa- tion effect of the biocomposite is not needed any more after the healing of the fracture, osteotomy, arthrodesis or the corresponding. In reconstructive surgery in filling bone defects, in changing the form of bone, in augmenting of bone etc. one can apply advantageously biocomposites, where at least the bioceramic component is biostable and tissue compatible and to which the cells of the growing bone tissue can be fixed. It is self-evident for specialists that also other com¬ binations of bioceramic components and material components than those shown in Figures 1 - 11 are possible and ef¬ fective in use in surgery. For all biocomposites of this invention is a common feature, however, that the bio¬ ceramic component and the material component have at least one common boundary surface, through which the pro- perties of the components are transmitted which gives strong, tough and secure biocomposites. The following non-limiting examples illustrate the pre¬ sent invention. Example 1. Biocomposites which are described in Figure 1 were manu¬ factured of nonporous (S) (no significant open porosity) or of porous (P) (open porosity 20 - 70 %) bioceramic plates (dimensions 30 x 10 x 4 mm) and of biostable or resorbable polymer reinforced with parallel fibres with the following methods: (1) A big polymer film sample (the thickness about 2 mm) was located on the surface of the bioceramic piece (BP) (on the 30 x 10 mm surface) so that the polymer film covered the whole surface of BP. The polymer film was pressed from above by means of a heated plate in such a way that the film melted and fixed tightly on the surface of BP. The thickness of the polymeric layer was then abou 1 mm. The biocomposite piece was cooled under pressure. (2) The reinforcement fibres were located on the surface of BP, a polymer film (the thickness about 2 mm) was placed on the reinforcement fibres and the film was com¬ pressed from above by means of a heated plate in such a way that the film melted, wetted the reinforcement fibres and penetrated to the surface of BP. The thickness of the material component (polymer and reinforcement) was the 1 mm and the weight fraction of the fibres about 40 %. The biocomposite was cooled under pressure. (3) The surface of BP was wetted with a polymer solution. The solvent was evaporated. This process was repeated so many times that a polymer layer with the thickness of 0.5 mm was obtained. (4) The reinforcement fibres were placed on the surface of BP. The fibres and the surface of BP were wetted with the polymer solution. A microporous Teflon-film was com¬ pressed on the surface of the sample. The solvent was evaporated. The polymer solution process was repeated so many times that a polymer-fibre layer with the thick¬ ness of 0.5 mm was obtained (the weight fraction of the fibres = 40 %) . (5) The surface of BP was wetted with reactive polymer system (with a monomer, oligomer or prepolymer or their mixture) . A 1 mm thick layer of reactive polymer was obtained on the surface of BP• (6) The reinforcement fibres were placed on the surface of BP. The fibres and the surface of BP were wetted with a reactive polymer system (a monomer liquid, oligomer, prepolymer or their■ mixture) . A 1 mm thick layer of reaction polymer-fibre mixture (the weight fraction of fibres = 40 %) was cured on the surface of BP. (7) The biocomposite was manufactured like above in the method (1) , but the polymer film contained 60 w-% sodium chloride powder (the average particle size 100 μm) . The biocomposite was immersed after manufacturing 6 h in distilled water at RT to dissolve the sodium chloride away. The biocomposite was dried, which gave a material with about 20 w-% of open porosity in its material component. (8) The biocomposite was manufactured like above in the method (2) but in addition by using sodium chloride powder as a filler of the polymer film to achieve open porosity to the material component like above in the method (7) . .(9) The biocomposite was manufactured like above in the method (3) but in addition by using in the polymer solution sodium chloride powder as an additive to achieve open porosity to the material component like above in the method (7) . (10) The biocomposite was manufactured like above in the method (4) but in addition by using in the polymer solution sodium chloride powder as an additive to achieve open porosity to the material component like above in the method (7) . (11) The biocomposite was manufcatured like above in the method (5) but in addition by using in the reactive polymer system sodium chloride powder as an additive to achieve open porosity to the material component like above in the method (7) . (12) The biocomposite was manufactured like- above in the method (6) but in addition by using in the reactive polymer system as an additive sodium chloride powder to achieve open porosity to the material component like above in the method (7) . The impact- and the bending strengths of the above com¬ posites were measured by means of the device and arran- ge ent shown schematically in Figure 12. The biocomposite sample (BP) was fixed of its both ends into a supporting bench (T) . The basic principle of the impact strength measurement was. to allow a pendulum of known mass to fall through a known height and strike the specimen at the lowest point of its swing and to record the height to which the pendulum continued its swing. The bending strength was measured by bending a biocomposite sample to its fracture with a constant speed (10 mm/mi . n) by a mov bending head from the middle of the sample according to Figure 12. The impact strength was calculated as the absorption of impact energy divided with the cross-sec- ■ tional ' area of the sample. The bending strength was calculated as the maximum bending load carrying capa¬ city of the sample in relation to its cross-sectional area. More accurate information of the arrangements of impact and bending measurements is given e.g. in the following book: Handbook of Plastics Test Methods, R'.'P. Brown (ed.), George Godwin Limited, London, Great Britain, 1981, Chapter 8. As reference values were used the impact and bending strength values which were measured with the identical measurement arrangements for the pure bio¬ ceramic pieces. Table 2 shows components and anufcaturing methods of some studied hydroxyapatite (HA) + polymer systems and HA + polymer composite systems (polymer + carbon fibre 40 w-%) . Table 3 shows the relative minimum and maximum impact strength and bending strength values of the studied composites (the strength values divided with strength values of the corresponding HA) . Table 2. Some biocomposites and their manufacturing methods. Four different biocomposites were manufactured of every polymer; Samples 1, 5, 9 etc.: porous HA + polymer, samples 2, 6, 10 etc.: porous HA + poly¬ mer +• carbon fibres (40 w-% fibres) , samples 3, 7, 11 etc.: nonporous HA +- polymer , samples 4, 8, 12 etc.: nonporous HA + polymer + carbon fibres. Sample 3) Manufacturing methods N:o Polymer of samples (N:σ) ' 1-4 High density polyethy¬ lene (HDPΞ) 1 , 2 5-8 Polypropylene (PP) 1 , 2 9-12 Polystyrene (PS) 1 , 2 13-16 Styreneacrylnitrile co- poly er (SAN) 1 , 2 17-20 Ξpoxide (EP) 5 , 6 21-24 Polyamide (PA) 1 , 2 25-28 Polyoximethylene (POM) 1 , 2 29-32 Phenylene oxide (PPO) 1 , 2 33-36 Polycarbonate (PC) 1 . 2 37-40 1) Polymethylmethacrylate (PMMA) 5 , 6 41-44 Polytetrafluoroethylene (PTFE) 1 , 2 45-48 Polysilicone (PSi) 1 , 2 49-52 Polyurethane (PU) 5 , 6 53-56 Polyarylate (PAr) 1 , 2 57-60 Polyether therketone (PEEK) 1 , 2 61-64 Polyester (PES) 1 , 2 65-68 Polyphelyne sulphide (PPS) 1 , 2 69-72 Polysulphone (PSu) 1 , 2 73-76 Polyethyleneterephthalate (PET) 1 / 2 77-80 Polyglycolide (PGA) 1 , 2 81-84 Poly-L-lactide (PLLA) 1 , 2 85-88 Poly-DL-lactide (PDLLA) 3 , 4 89-92 Glycolide/lactide copolymer (PGA/PLA) 1 , 2 93-96 Glycolide/trimethylenecarbo- nate copolymer (PGA/TMC) 1 , 2 97-100 Polyhydroxybutyrate (PHBA) 3 , 4 101- 04 Hydroxybutyrate/hydroxyvale- rate copolymer (PHBA/PHVA) 1 , 2 105-108 Poly-p-dioxanone (PDS) 3 , 4 109-112 2) Polyesteramide (PEA) 1 , 2 113-116 Poly-ε-caprolactone 1 , 2 117-120 Poly-δ-valerolactone 1 , 2 121-124 Polyetherester 1 , 2 125-128 Chitine polymer 3 , 4 1 ) Bone cement 2) The structural a n u formula of -0-CH 2 ~C-NH- (CH 2 ) 2 -NH-C-CH 2 "0-C- (CH 2 ) 12 polymer: 3) In the case of every polymer the first manufacturing method was applied to do nonreinforced samples and the second method to do fibre reinforced samples. Table 3. The strength regions of biocomposites of Table 2. •' Material Relative impact Relative bendin strengths strengths 1.1-2 Porous HA + polymer 3.5-40 1.6-6 Porous HA + reinforced 120-240 polymer Nonporous HA + polymer 1.1-4.2 1.1-1.6 Nonporous HA + reinforced 1.8-20 1.1-3.5 polymer It was found that the strengths of all fibre reinforced composites were clearly better than the strengths of HA or of HA coated only with a polymer. Example 2. The manufacturing method (2) of example 1 was applied to manufacture biocomposites shown schematically in Figure 1a. The used materials were: nonporous (S) and porous (P) (open porosity 20-70 %) bioceramic plates (dimensions 30 x 10 x 4 mm) and resorbable polymer com¬ posites. Table 4 shows some mechanical strength measu¬ rement values for biocomposites where hydroxyapatite ceramics were applied as bioceramic components. The relative impact and bending strength values of biocompo¬ sites were obtained by dividing the strength values of biocomposites with the corresponding strength values of pure hydroxyapatite bioceramics. Table . Properties of biocomposites Sample Bioceramic Polymer Reinforcement 5) The relative strength of the biocompos N:o component component fibres of po¬ lymer component Impcat strength Bending strength I, 2 HA; 1) P and 2) (S) PGA PGA 3) 120 4) (20) 3) 3 ~ ' (1.4) 3, 4 PLLA PGA 110 (32) 3.2 (1.8) 5, 6 PDLLA PLLA 140 (40) 2.8 (2.0) 7, 8 PHBA PGA 135 (35) 2.6 (1.8) 9, 10 PDS PGA 200 (65) 2.1 (1.6) II, 12 PDS PLLA 220 (80) 2.2 (1.8) 13, 14 PEA PLLA 185 (65) 1.8 (2.0) 1) Porous (open porosity about 60 %) 2) Nonporous (no significant open porosity) 3) The values of biocomposites containing porous bioceramic components 4) The values of biocomposites containing nonoporous bioceramic components 5)'The thickness of the reinforced material component about 0.4 mm Several porous bioceramics (porosity 40-70 %) and the po¬ lymers and fibre reinforcements of Table 4 were applied to manufacture corresponding biocomposites to those shown in Table 4. The following bioceramics were used: tricalciumphosphate, dicalciumphosphate, magnesium/calciu phosphate, fluoroapatite, aluminiumoxide and calcium- carbonate. The relative impact strengths of these bio¬ composites varied between between 85 and 220 and the relative bending strengths between 1.4 and 3.8. When the corresponding composites were manufactured without fibre reinforcement of the polymer component the strength values varied between 2 and 12 (the relative impact strength) and between 1.0 and 1.6 (the relative bending strength) . Example 3. A bioceramic piece with dimensions of 30 x 10 x 3 mm was placed intoan injection moulding mould (the dimen- • sions of the inner cavity of the mould were 30 x 10 x 4 mm) . The empty space (30 x 10 x 1 mm) inside of the mould cavity above the bioceramic sample was filled with a melt of liquid crystalline thermoplastic polymer (ma¬ nufacturer Celanese Inc., trade name Vectra: injection moulding quality) in such a way that the polymer melt ■ filled the empty space of the mould and was fixed to the bioceramic piece. The mould was cooled and opened and a biocomposite sample with dimensions of 30 x 10 x 4 mm was obtained with a bioceramic component and the liquid crystalline polymer component. Following bioceramics were applied in manufacturing bio- composites: hydroxyapatite (nonporous and porous mate¬ rials), fluoroapatite, tricalciumphosphate, dicalcium¬ phosphate, magnesium/calciumphosphate, an alloy of hydr¬ oxyapatite and tricalciumphosphate, aluminiumoxide, bioglass 45S, a glass ceramic containing apatite (MgO- CaO-Si0 2 ~P 2 0 5 -CaF) and CaCO... The porosities of biocera- mics were between 20 and 70 % in the different cases. The relative impact and bending strengths of the above biocomposites were measured according to Example 1 and Figure 12. In the case of biocomposites containing po- rous bioceramic -components the relative impact strengths were between 80 and 180 and the relative bending strengths between 3 and 8. The materials containing solid bioceramic components showed the relative impact strengths 6 - 30 and the relative bending strengths 1.4 - 2.4. Example 4. Porous calciumcarbonate (CaCO,) pieces (porosity about 70 %, the dimensions 40 x 12 x 12 mm) were applied to manufacture according to the methods 3 (and 4) of Example 1 biocomposites whose principal structure is given in Figure 1. The following biocomposites were manufactured: Sample 1 = pure CaCO-., Sample 2 = CaCO, whose one long surface is coated with 0.5 mm thick lay -er of PLLA (Mw = 260 000) , Sample 3 = CaCO, + one long surface is coated with 0.5 mm thick layer of PDS, Sample 4 = CaCO, ÷ one long surface is coated with 1 mm thick layer of PDS which is reinforced with 0.5 mm thick PGA/PLLA fibre fabric (the fibre content of polymeric material component = 40 vol.-%) , Sample 5 = like Sample 4 but all the long surfaces of the CaCO piece are coated with the fabric, Sample 6 = filament wound sample: CaCO, piece was coated by winding on it 0.5 mm thick layer of PLLA fibres coated with PDLLA (the winding temperature 150°C, the thickness of fibre bundle = 0.1 mm, the amount of filament wound layers of fibre bundles on the surface of bioceramic was 5) , Sample 7 = filament wound sample like Sample 6 but noncoated PLLA fibres were applied as reinforcing material component. Table 5 shows the relative strength values of Samples 1 - 7 when compared.to the strength values of pure CaCO,. Table 5. The relative strengths of Samples 1 - 7 Sample N:o Impact strength Bending strength 1 1 1 2 2 1.8 3 2 . 4 1.4 4 1 90 2.2 5 460 9.5 6 800 35 7 560 2.0 Example 5 . Biocomposites whose structure is given principally in Figure 1b were manufactured according to the method (4) of Example 1 of porous hydroxyapatite (open porosity 60 %) and of PLLA, which was reinforced with diffe¬ rent biostable fibres (the fraction of fibres in compa¬ rison to PLLA 40 %) . Table 6 shows the applied reinforce¬ ment fibres and the relative impact strengths of bio¬ composites (when compared to the impact strength of porous HA) . Table 6. The relative impact strengths of HA-PLLA-fibre composites. Sample N:o Reinforcement fibres Relative impact of material component strengths 1 E-glass fibres 220 2 Carbon fibres 160 3 Ara ide fibres 380 4 Aromatic polyester 400 fibres Example 6. Cylindrical biocomposite samples whose structure is given principally in Figure 7a were manufactured of porous hydroxyapatite (HA) (sample dimensions: height 3 mm, diameter 6 mm, degree of porosity 50 %) , of poly¬ lactide polymer and of polylactide reinforcement fibres in the following manner. PLLA fibre bundles coated with PDLLA melt were wound rapidly on the cylindrical surface of HA-cylinders so that a homogeneous PLLA fibre reinforced PDLLA coating was achieved on the cylindrical surface of HA-pieces. The upper and lower surfaces of biocomposite cylinders were left free. The cylindrical biocomposite samples were implanted between vertebrae C3-4, C4-5 or C5-6 of rabbits to replace the intervertebral discs. Normal aseptic operation techniques were applied. The movement of biocomposite plates was prevented anteriorly be means of resorbable sutures which were tightened between the vertebrae. Altogether 22 implants were implanted in 14 rabbits. The position of implants and the progress of fusion was followed radiographically in three weeks periods. As a reference series were six rabbits, into which were implanted nine porous HA-cylinders without reinforced polymeric surface layer. During the implantation of the biocomposites of this invention the operations proceeded without problems and all the implantations healed in a good or satisfac¬ tory manner without any radiographical observation of breaking of biocomposite cylinders or any significant partial extrusion of samples from the intervertebral space. In the reference series two HA-cylinders were broken during implantation operation, several cylinders were broken during healing and were extruded at least par¬ tially from the intervertebral space into the sur¬ rounding soft tissue. This showed clearly the surprising advantages of the biocomposite of this invention in comparison to the pure HA-cylinder. Example 7 . Cylindrical, layered biocomposites whose structure is given schematically in Figure 7b were manufactured of porous (porosity about 50 %) hydroxyapatite (HA) tubes (length 30 mm, outer diameter 2.6 mm, inner diameter 1.6 mm) by filling the inner cavity of tubes with polymer components in the following way: (1) The inner cavity of the tube (Layer 2) was filled with the polymer melt (Layer 1) by melt moulding and the biocomposite was cooled. (2) The self-reinforced resorbable polymer composite rod or the polymer composite rod reinforced with biostable fibres was immersed in a solution of resorbable polymer (10 % w/v solution) and the rod was tapped rapidly into HA-tube and the biocomposite was dried. The dimensions of rods were: diameter 1.5 mm, length 30 mm. (3) The biocomposite rods which were manufactured with the above method (2) were coated with resorbable polymer (Layer 3) by immersing the biocomposite rods into a solution of resorbable polymer (> 5 % w/v solution) and by drying the samples. This operation was repeated so many times that the resorbable surface layer with thick¬ ness of 0.1 mm was achieved. (4) Biocomposite rods of the above method (2) were coated with a solution of resorbable polymer (5 % w/v solution) which contained sodium chloride powder (average particle size 100 μm) so that the amount of sodium chloride powder was about 40 w-% of the weight of the dry polymer. The rods were coated with 0.15 mm thick polymer-sodium chloride layer. TJhe- solvents were evaporated in vacuum. The sodium chloride was dissolved in distilled water and the bio¬ composite rods were dried. Accordingly these polymer composite rods comprised of a surface layer of resobable 34 polymer with open porosity, of a porous HA-tube and of a self-reinforced core inside of the HA-tube. Table 7 shows the relative impact and bending strength values of the manufactured biocomposite rods in compa¬ rison to the corresponding strength values of HA-tubes. Table 7. The relative strength values of cylindrical biocomposites Sample Manuf. Layer Layer Layer Relative strengths N:o " method 1 2 3 Impact Bending (Ex. 7) strength strength 1 • - - HA - 1 1 2 1 HDPΞ - 35 16 3 2 self- _ιι β 180 60 reinf. PLLA 4 3 —_ !l -_. - " PLLA 230 65 * 5 4 II II "ll 195 65 Example 8. Biocomposite rods of Table 7 (Samples 1 - 5) were manu¬ factured according to Example 7. Additionally cylindri¬ cal rods with length 30 mm, diameter 2.6 mm were injec¬ tion moulded of-PLLA containing -30 'W-% HA-powder (par¬ ticle size between 10 μm and 200 μm) (Sample N:o 6) . The samples were located in mandibles of rabbits between both sides of ostectomized inferior borders of the mandible through the soft tissues under the mylohyoid muscle. The porous HA-tubes (Sample 1) were broken easily during the operation and part of them was broken also during the early follow-up period after the operation (during one week after operation) . All the biocomposite samples and Sample N:o 6 remained unbroken during the operation and during the follow-up (6 months) . Radiographic studies showed new bone formation along the 35 surfaces of the implanted materials and into their pos¬ sible open porosity from both sides of ostectomized man¬ dible. Clear variations in osteoconductivity of diffe¬ rent materials could be seen because the growth rates of new bone on the surfaces of the rods had the following order: rapid slow Sample 1 = Sample 2 = Sample 3 > Sample 5 > Sample 6 > Sam Example 9. Following bioceramics were applied to manufacture porous (open porosity 40 - 60 %) and nonporous, thin, plate-like samples (dimension 20 x 5 x 1 mm) : hydroxyapatite, tri¬ calciumphosphate, dicalciumphosphate, aluminiun oxide, biogalss (Bioglass 45S) and calciumcarbonate. The plates were coated with PLLA, which contained 40 w-% of bio¬ stable glass fibres (E-glass) or biodegradable glass fibres (calciumphosphate fibres) as reinforcing elements (plates were made as in Example 1 , method 4) . The relative impact strengths of biocomposites were 80 - 600 and 30 - 200 in the case of biocomposites with porous- and nonporous bioceramic components respectively. The cor¬ responding relative bending strengths of biocomposites were 15 - 40 and 1.2 - 4 in comparison to the strength values of corresponding porous and nonporous bioceramic components, respectively. Example 10. Porous hydroxyapatite (HA)) tubes (open porosity about 50 %, the outer diameter 11 mm, the inner diameter 9 mm and the length 60 mm) were coated by filament winding with PLLA fibre bundle which was coated with PDLLA. The thickness of the fibre bundle was 0.1 mm. PDLLA/PLLA relation was 50/50. The fibre bundles were wound on the tubes according to the principles of Figure 8c at about 150°C temperature. The thickness of the reinforced poly¬ meric coating was 2 mm. The surface of the coating was compressed smooth in a cylindrical heated mould. Corresponding coated HA-tubes were manufactured by melt moulding on the HA-tubes 2 mm thick layers of PDLLA po¬ lymer in an injection moulding mould. The impact and bending strengths were measured 1) for HA-tubes, 2) for PDLLA-coated HA-tubes and 3) for PDLLA/PLLA(fibre rein¬ forcement)-coated HA-tubes. Table 8 shows the relative strength values. Table 8. Relative strength values of HA-tubes and HA-PLA- composite materials. Sample Relative strength values N:o Material Impact str. Bending str, 1 HA-tube 1 1 2 PDLLA-coated HA-tube - 40 8 3 PDLLA/PLLA(fibre rein¬ 760 75 forcement)-coated HA-tube

Claims: CLAIMS 1. Biocomposite material for bone surgical applications, which biocomposite comprises: - at least one bioceramic piece (1) (bioceramic component) and - at least one material component (2) which has been manufactured of at least one polymer or corresponding, which material component (2) has at least one common boundary surface with the bioceramic component, c h a r a c t e r, i z e d in that - the material component (2) comprises at least reinforce¬ ment elements which have been manufactured of essen¬ tially resorbable material like polymer, copolymer, polymer mixture and/or ceramic material and that - the material component (2) can include binding material which is manufactured essentially of resorbable polymer, ' copolymer or polymer mixture and that - the material component (2) contains at least in tissue . conditions open porosity. 2. A biocomposite material according to Claim 1, c h a ¬ r a c t e r i z e d in that the bioceramic component contains at least partially open porosity and that the material component (2) has a connection with the bioceramic component in such a way that at least part of the open porosity of the bioceramic component (1) is free of the material component (2) . 3. A biocomposite material according to Claims 1 and/or 2, c h a r a c t e r i z e d in that the material component (2) comprises at least reinforcement elements, like fibres or film fibres or structures which have been constructed of them, which reinforcement elements have been manufactured at least of one the following resorbable polymers: polyglycolides (PGA) , polylactides (PLA) , glycolide/lactide copolymers (PGA/PLA) , glycolide/ trimethylenecarbonate copolymers (PGA/TMC) , poly-β-hydroxy- butyric acid (PHBA) , poly-β-hydroxypropionic acid (PHPA) , poly-β-hydroxyvaleric acid (PHVA) , PHBA/PHVA copolymers, poly-p-dioxanone (PDS) , poly-1 ,4-dioxanone-2 ,5-diones , polyesteramides (PEA) , poly-ε-caprolactone. poly-δ- valerolactone. polycarbonates, polyesters of oxalic acids, glycolic esters, dihydropyrane polymers, poly- etheresters, cyanacrylates or chitine polymers. 4. A biocomposite material according to Claims 1 - 3, c h a r a c t e r i z e d in that the binding material of the material component (2) has been manufactured at least of one of the following resorbable polymers: poly¬ glycolides (PGA) , polylactides (PLA) , glycolide/lactide copolymers (PGA/PLA) , glycolide/trimethylenecarbonate copolymers (PGA/TMC) , poly-β-hydroxybutyric acid (PHBA) , poly-β-hydroxypropionic acid (PHPA) , poly-β-hydroxyvaleric acid (PHVA), PHBA/PHVA copolymers, poly-p-dioxanone (PDS) , poly-1 , 4-dioxanone-2,5-diones, polyesteramides (PEA) , poly-ε-caprolactone, ■ poly-d-valerolactone, polycarbonates , polyesters of oxalic acid, glycolic esters, dihydropyrane polymers, polyetheresters, cyanoacrylates or chitine polymers. 5. A bioomposite material according to ' Claims 1 - 4, c h a r a c t e r i z e d in that the bioceramic com¬ ponent (1) has been manufactured at least of one of the following bioceramics: calciumphosphates (like tricalcium- phosphates) , dicalciumphosphates, apatites (like hydroxy- apatites or fluoroapatites) and magnesiumcalciumphos- phates, the mixtures of hydroxyapatite and tricalcium¬ phosphate, aluminiumoxide ceramics, bioglasses, glass ceramics containing apatites (like MgO-CaO-Si0 2 -P 2 0 5 -CaF) or calciumcarbonate. 6. A biocomposite material according to Claims 1 - 5, c h a r a c t e r i z e d in that the bioceramic com¬ ponent (1) of the biocomposite is a plate, a rod, a prism (like a cube etc.) , a cylinder, a tube or a chute or it has been designed to correspond anatomically some bone or some part of a bone and that the ma¬ terial component (2) has been located on at least one surface of the bioceramic component. 5 7. A biocomposite material according to Claim 1, like a rod or an intermedullary nail for fixation of bone fractures, osteotomies and arthrodesis, c h a r a c ¬ t e r i z e d in that it comprises a tube-like or rod¬ like ceramic component (1 ) and a material component 10. (2) comprising a resorbable polymeric binding material and resorbable fibrous reinforcement elements, which material component (2) has been wound on the surface of the ceramic component ( 1 ) . 8. A biocomposite material for fixation of bone fractures, 5 osteotomies and arthrodesis and for reconstruction of bone tissue according to Claim 1 , c h a r a c t e r i z e d in that it comprises a plate-like bioceramic component * (1) , whose upper- and/or lower surface and/or side sur¬ faces have been coated with a material component (2) , 0 which comprises a resorbable polymeric binding -material and resorbable fibrous reinforcement elements. 9. A biocomposite material according to Claim 8, c h a - r a c t e r i z e d in that the material has been orga¬ nized to a layered sample, where the bioceramic corapo- 5 nents (1) and material components (2) alternate. 10. A biocomposite material according to Claim 8, c h a ¬ r a c t e r i z e d in that the bioceramic component (1) has been grooved (Figure 3) . 11. A method to manufacture a biocomposite, c h a r a c - 0 t e r i z e d in that the bioceramic component (1) is coated at least partially by using as a coating agent continuous reinforcement fibre, reinforcement fibre bundle or a thread manufactured of cut fibres etc. , which rein- forcement structure can be coated with a polymer or can be wetted with a polymer on the surface of the bioceramic component and which reinforcement fibre, -bundle or thread is brought to the surface of the bioceramic compo- nent by using the filament winding method in such a awy that the bioceramic component and/or the guide which feeds the reinforcement elements rotates around at least one axis and/or moves in the direction of at least one axis. 12. Application of the biocomposite materials according to Claims 1 - 10 to fill a defect, a hole or corresponding n a bone, to augment bone tissue, to change the bone tissue, or in other reconstructive bone surgery or in fixation of bone fractures, osteotomies, arthrodesis or joint damages.

Inventors: HELEVIRTA PERTTI, PELLINEN MARJA, ROKKANEN PENTTI, TOERMAELAE PERTTI, VAINIONPAEAE SEPPO, HELEVIRTA, PERTTI, PELLINEN, MARJA, ROKKANEN, PENTTI, TOERMAELAE, PERTTI, VAINIONPAEAE, SEPPO
Applicants: MATERIAL CONSULTANTS OY
Application year: 1987
Main classification: A61L27
IPC codes: A61F2, A61L26, A61L27, A61L31