for the generation of the osteogenic matrix composite , a solution of collagen monomers in 0 . 01 m acetic acid is prepared by stirring for 24 hours at 4 ° c . the collagen fibrils are subsequently formed in the presence of the noncollagenic components by a process of self - aggregation ( fibrillogenesis ) in aqueous phosphate buffer solutions at neutral ph and a temperature of 37 ° c . the range for the formation of the fibrils is between 0 . 5 and 5 mg of collagen / ml and 0 . 1 to 5 mg of glycosaminoglycan / ml , 1 mg / ml of collagen and 0 . 2 mg / ml of gag and 30 μg / ml of proteoglycan being the preferred conditions . the preferred fibrillogenesis parameters were a 30 mmol / l phosphate buffer ph 7 . 0 , either with 135 mmol / l of nacl or without nacl addition . glycosaminoglycans or other matrix components are added to the collagen monomers before fibrillogenesis and thereby integrated at least partially into the resulting fibrils in the following process of fibrillogenesis . fig1 shows , in a measurement of the turbidity of a solution caused by fibril formation , over time , that increasing amounts of decorin ( indicated in molar ratios ) cause a slowing of the formation kinetics and a reduction of the maximum od values , indicative of a reduction of the fibril diameter . for chondroitin sulfate , an opposite effect is to be observed . formation conditions : 250 μg / ml of collagen , 37 ° c ., 30 mmol / l of phosphate buffer ph 7 . 4 containing 135 mmol / l of nacl . in fig2 , the influence of the formation conditions on the structure of the resulting fibrils is documented in afm photographs . addition of decorin reduces the fibril diameter ( a and d ) under all conditions . for chondroitin sulfate , in particular under conditions of low ionic strength , a markedly more heterogeneous distribution of the fibril diameter is visible with increase in the average fibril diameter ( f ), while the effect is not apparent at higher ionic strengths ( c ). b and e show the fibril structure without noncollagenic additives . formation conditions : 250 μg / ml of collagen , 37 ° c ., 30 mmol ./ l of phosphate buffer ph 7 . 4 ( buffer a ) or 30 mmol / l of phosphate buffer ph 7 . 4 containing 135 mmol / l of nacl ( buffer b ). in all cases , however , during fibrillogenesis in vitro the collagen monomers form the characteristic transversely striated fibrils analogously to the in vivo structures , the structure of the resulting fibrils being influenced both by the process parameters ( ph , ionic strength , phosphate concentration ) and by the nature and amount of the added noncollagenic components . collagen fibrils containing noncollagenic constituents such as glycosaminoglycans or decorin can accordingly be produced in a comparatively wide range of mass ratios , within which the integration of the collagen into the fibrils is not or is only slightly influenced . for generation of the osteogenic matrix composite , a solution of collagen monomers in 0 . 01 m acetic acid is prepared by stirring at 4 ° c . for 24 hours . the collagen fibrils are subsequently formed by a process of self - aggregation ( fibrillogenesis ) in aqueous phosphate buffer solutions at neutral ph in the presence of the noncollagenic components . formation conditions : 250 μg / ml of collagen , 37 ° c ., 30 mmol / l of phosphate buffer ph 7 . 4 ( buffer a ) or 30 mmol / l of phosphate buffer ph 7 . 4 containing 135 mmol / l of nacl ( buffer b ) with different chondroitin sulfate and decorin concentrations . after washing and hydrolysis of the fibrils in 500 μl of 6 m hcl at 105 ° c . for 6 hours , decorin and chondroitin sulfate integrated into the fibrils was determined according to the method of pieper et al . [ pieper j s , hafmans t , veerkamp j h , van kuppevelt t h . development of tailor - made collagen - glycosaminoglycan matrices : edc / nhs crosslinking , and ultrastructural aspects . biomaterials 2000 ; 21 ( 6 ): 581 - 593 ]. for chondroitin sulfate , the extent of the integration is dependent on the ionic strength of the buffer system . used . for low ionic strengths ( buffer a ), of the 20 μg employed , about 2 . 5 μg of cs are incorporated on 250 μg of collagen , for high ionic strengths ( buffer b ), however , only a third of this amount ( fig3 ). the incorporation of decorin also depends on the buffer system used . for buffer a , a third of the amount employed is incorporated , while the values for buffer b were again markedly lower . recruitment of growth factors by an implant coated with an osteogenic matrix composite matrices composed and produced according to the invention can accelerate and improve bone formation and accumulation without the use of recombinant growth factors by the recruitment of endogenous growth factors . in the experiment , such a binding behavior can only be demonstrated using recombinant growth factors . a sandblasted , cylindrical sample of tial6v4 having a diameter of 10 mm is cleaned with ethanol , acetone and water . a solution of 1 mg / ml of bovine collagen type i in 0 . 01 m acetic acid is produced by stirring overnight at 4 ° c . noncollagenic ecm components ( glycosaminoglycan 30 μg / ml , proteoglycans 15 μg / ml ) are added to this solution . the mixtures are treated with fibrillogenesis buffer ( 60 mmol / l of phosphate , 270 mmol / l of nacl , ph 7 . 4 ) on ice and incubated at 37 ° c . for 18 h . the resulting fibrils are centrifuged off , washed , homogenized and resuspended to give a final concentration of 1 mg / ml . the cylindrical sample is coated ( dip - coating ) with this solution at rt for 15 min , washed with water and dried . subsequently , growth factors ( recombinant bmp - 4 or tgf - 1β ) are immobilized on these - surfaces by an adsorption process ( 4 ° c ., 18 h , from pbs ) and subsequently . determined by means of elisa . these in vitro tests with recombinant growth factors show that by the addition according to the invention of noncollagenic components , the binding of the growth factors rhbmp - 4 ( in particular by addition of chondroitin sulfate ) or rhtgf - 1β ( in particular by addition of decorin ) to the matrix is increased . for bmp , with small amounts ( 2 - 20 ng / cm 2 ) no effect is observed , with higher amounts ( from 50 ng / cm 2 ), however , an approximately 10 % higher binding to the chondroitin sulfate - containing layer occurs , compared with the pure collagen layer , shown in % of the amount employed ( fig4 ). for rhtgf - 1β , increased binding is detectable on decorin - containing surfaces both for 1 ng / cm 2 and for 10 ng / cm 2 . formation conditions of the matrix : 500 μg / ml of collagen , 30 μg / ml of decorin and / or chondroitin sulfate , 37 ° c ., 30 mmol / l of phosphate buffer ph 7 . 4 containing 135 mmol / l of nacl . fig5 shows the behavior of primary rat calvaria osteoblasts on various matrices . initial adhesion of the cells to different matrix compositions was analyzed by means of cell morphology , cytoskeletal organization ( actin staining with phalloidin ) and formation of the focal adhesion complexes by means of integrin receptors ( immunostaining against vinculin ). adhesion was most pronounced after 2 hours on collagen - cs matrices followed by collagen - decorin . the formation of the facs ( green - yellow dots and red on the ends of the actin fibrils ) was also promoted and accelerated by decorin and particularly cs . controls using pure collagen matrices showed significantly less facs after 2 hours . the influence of the matrix composition on the differentiation of the osteoblasts was investigated by means of the expression of the marker protein osteopontin by means of fluorescence - activated cell scanning . osteoblasts on collagen - cs surfaces produced 5 times more osteopontin (˜ 2500 fluorescence units ) after 8 days than cells on pure collagen surfaces (− 500 fluorescence units ). formation conditions of the matrix : 500 μg / ml of collagen , 30 μg / ml of decorin and / or chondroitin sulfate , 37 ° c ., 30 mmol / l of phosphate buffer ph 7 . 4 containing 135 mmol / l of nacl . further investigations with rat calvaria osteoblasts showed different cell reactions on rhbmp - 4 depending on the composition of the carrier matrix . fig6 shows the activity of the alkaline phosphatase in activity units u per mg of protein after addition of 4 pmol / cm 2 of rhbmp - 4 to rat calvaria cells . on decorin - containing matrices , the bmp activity is underregulated , while on chondroitin sulfate - containing matrices it is increased . formation conditions of the matrix : 500 μg / ml of collagen , 30 μg / ml of decorin and / or chondroitin sulfate , 37 ° c ., 30 mmol / l of phosphate buffer ph 7 . 4 containing 135 mmol / l of nacl . in animal experiments , it was surprisingly found that matrices provided with recombinant growth factors perform markedly more poorly with respect to induced bone formation than the noncrosslinked osteogenic matrix composites according to the invention based on collagen type i and chondroitin sulfate . ti implants , which have annular incisions at right angles to the axis and thus represent a defect model , are cleaned with 1 % triton x - 100 , acetone and 96 % ethanol , rinsed with distilled water and dried . the implants employed are coated in two successive dip - coating steps with : a . fibrils of collagen type i , b . osteogenic matrix composite according to the invention based on collagen type i and chondroitin sulfate according to working example 1 c . osteogenic matrix composite according to the invention based on . collagen type i and chondroitin sulfate according to working example 1 the implants are washed with distilled water , air - dried and sterilized with ethylene oxide at 42 ° c . for 12 h . immediately before implantation , the surface condition c is coated overnight with recombinant bmp - 4 ( 400 ng / ml ) at 4 ° c . and subsequently dried . the implants are employed in the lower jaw of minipigs . the bone implant contact was determined histomorphometrically after 6 months . the highest percentage for this contact is obtained for implants coated with the osteogenic matrix according to the invention based on collagen and chondroitin sulfate ( 27 . 8 %), while implants with the same coating and recombinant bmp - 4 and the combination were around 15 % and thus markedly lower . the lowest values are obtained for the pure collagen coating ( 12 . 8 %) ( fig7 ). bfgf basic fibroblast growth factor bmp bone morphogenetic protein ecm extracellular matrix egf endothelial growth factor facits fibril associated collagen with interrupted triple helix facs focal adhesion contacts fgf fibroblast growth factor gag glycosaminoglycan hap hydroxylapatite igf - i insuline - like growth factor pga polyglycolic acid pla polylactic acid slrp small leucine - rich protein tcp tricalcium phosphate phases tes ( n -[ tris ( hydroxymethyl ) methyl ]- 2 - aminoethanesulfonic acid ) tgf - β transforming growth factor β vegf vascular endothelial growth factor wf growth factor
the invention relates to an osteogenic composite matrix consisting of collagen and non - collagen components of an extracellular matrix , to a method for producing said matrix , to a method for producing an implant or a scaffold for tissue engineering which is provided with a coating formed by said osteogenic composite matrix and is used for stimulating and accelerating a hard tissue formation such as , for example the implant osseointegration in bones . the inventive osteogenic composite matrix comprises a collagen and at least one non - collagen ecm component or the derivatives thereof , wherein the collagen component consists of non - crosslinked collagen fibres produced by fibrillogenesis and the non - collagen ecm component or the derivatives thereof are integrated into said collagen fibres .