a ) a particulate component that is difficult to dissolve in water , and , b ) at least one liquid or gel component that is soluble in water , so that a paste - like mixture is formed . the hydrogel component that dissolves more easily acts as an intrinsic pore former in the bone defect . the intermediate spaces between the particles of the preparation , the size of which is a function of the particle size and the particle size distribution , promote the ingrowth of veins and tissue . the hydrogel matrix that dissolves more easily also expands the agglomeration of the particles and simultaneously promotes cohesion in order to assure injectability . as fig1 depicts , the hydrogel matrix ( 1 ) is located between the particles ( 2 ). when the inventive preparation is inserted into the defect , blood ( 3 ) coagulates , calcium - indicated , on the surface of the agglomeration of the particles , which is depicted schematically in fig2 . the hydrogel component that dissolves more easily is resorbed within a short period of time so that the particle agglomeration stabilized by fibrous tissue remains . this agglomeration made of resorbable bioceramic having large interparticulate intermediate spaces now satisfies all requirements for a bone replacement material in terms of porosity , freedom from phase shift , and resorbability . the following is understood for the term not easily soluble . the not easily soluble substance dissolves in water at room temperature in a maximum concentration of 100 mg / l . in accordance with the invention , the particles in the preparation have a size in the range from 0 . 1 to 150 μm , pores having a diameter of 0 . 01 - 50 μm , and can comprise β - tricalcium phosphate , α - tricalcium phosphate , whitlockite , octacalcium phosphate , hydroxyapatite , type a carbonate apatite , type b carbonate apatite , calcium - deficient hydroxyapatite , amorphous calcium phosphate , and / or resorbable glass ceramics . the calcium phosphate particles can have both a round shape and a polygonally broken shape that is rounded by wear and thermal sintering . the aforesaid particles in the size range of 0 . 1 to 150 μm have pore diameters of 0 . 01 to 50 μm . the inventive , plastically deformable preparation can be paste - like or can have a very viscous , more kneadable to wax - like form . the paste - like form of the preparation is designed such that it can be applied to a bone defect in a minimally invasive manner by means of an injection syringe having a straight or angled cannula . the diameters of the particles are optimized for the cannula diameter of an injection cannula . particle diameters are optimized such that the paste - like material can also be applied using an cannula that is angled up to 60 °, measured with respect to the longitudinal axis of the injection syringe . it is essential for the invention that it is constructed from a mixture of 60 - 90 % by mass calcium phosphate particles and 1 - 30 % by mass of an aqueous or alcoholic solution of dextran and / or carboxymethyl dextran and / or hyaluronic acid and / or dermatan sulfate , carboxymethyl cellulose and / or oxidized cellulose and / or gelatins and / or mixtures thereof . the use of polysaccharide derivatives , such as for instance carboxymethyl dextran , carboxymethyl hyaluronic acid , and sulfated hyaluronic acid , is also within the sense of the invention . it is likewise inventive that it is preferably constructed from a mixture of 80 - 98 % by mass calcium phosphate particles , 1 - 20 % by mass anhydrous polyethylene glycol 400 , and 1 - 20 % by mass anhydrous polyethylene glycol 600 . polyethylene glycol 400 and polyethylene glycol 600 can also contain oxidation stabilizers , in addition . fig3 provides detailed images of the x - ray powder diffractograms of ( 1 ) the initial batch of a β - tcp ceramic ( 2 ) β - tcp in hyaluronic acid solution ( 3 ) β - tcp in dextran solution ( 4 ) β - tcp in methylcellulose solution after 12 weeks &# 39 ; storage in water . as can be seen from this documentation , in the inventive formulation there is no conversion to a different phase of the calcium phosphate family . fig4 provides detailed images of the x - ray powder diffractograms of ( 1 ) the initial batch of a β - tcp ceramic ( 2 ) the same ceramic after 12 weeks &# 39 ; storage in water as can be seen from this documentation , in the aqueous suspension there was partial conversion / recrystallization of β - tcp to hydroxyapatite . the inventive preparation can be sterilized with dry heat or using gamma rays at a dosage of 8 to 30 kgy (= kilograys ). the hyaluronic acid used for the inventive preparation or the hyaluronic acid salts can be bioengineered , the hyaluronic acid having a molecular weight of 1 , 500 , 000 to 4 , 500 , 000 daltons and sterilization reducing this to 700 , 000 to 2 , 500 , 000 daltons . the invention shall be explained using examples in the following , but the invention shall not be limited to these examples . components a through k can be used for producing the plastically deformable implant material . 99 % β - tricalcium phosphate , free of phase shift , polygonally broken , the broken edges rounded by abrasion and subsequent burning , having a porosity of 20 ± 5 % and particle size distribution of 0 . 1 - 50 μm , bulk density of 1 . 1 ± 0 . 1 g / cm 3 , and grain size of & lt ; 63 μm ( d 50 = 15 ± 5 μm ) 0 . 3 g component a are added to 20 . 05 g component c . after a 4 - hour swelling time , the gel is sterile - filtered , slowly added to a total of 50 g component b , and mixed intimately . the mixture is sterilized in a container at 121 ° c . using dry heat . the result is a homogenous mixture with a paste - like consistency that is easily extruded through a cannula , conforms to a defect due to plastic flow , and that air easily hardens superficially , it being possible to accelerate this process using a gentle airflow from a compressed air pistol . after heat sterilization the material has a molecular weight of 1 . 7 ± 0 . 5 mda . even after 4 hours of centrifuging , no solid or liquid settles out . an extruded paste adheres well to surrounding tissue . an extruded and superficially dried body retains its shape in the simulated body environment ( moist chamber under physiological conditions ). 0 . 2 g component a are added to 20 . 0 g component c . after a 4 - hour swelling time , the swollen gel is sterile - filtered , slowly added to a total of 63 . 4 g component b while stirring , and mixed intimately . the mixture is sterilized in a closed container at 121 ° c . using dry heat . the result is a homogenous mixture that has a plastic consistency and is kneadable , that because of its kneadability is easily applied to a bone defect , that adheres well to the surrounding tissue , and that air easily hardens superficially , it being possible to accelerate this process using a gentle airflow from a compressed air pistol . after sterilization the material has a molecular weight of 1 . 7 ± 0 . 5 mda . even after 4 hours of centrifuging , no solid or liquid settles out . a hand - formed and superficially dried body retains its shape in the simulated body environment ( moist chamber under physiological conditions ). 225 mg component d are added to 38 mg component a , and then 9 . 7 g component c is added while stirring . after a 1 - hour swelling time , the swollen gel is sterile - filtered , slowly added to a total of 22 g component b while stirring , and mixed intimately . the mixture is sterilized in a closed container at 121 ° c . using dry heat . the result is a homogenous mixture with a paste - like consistency that is easily extruded through a cannula , conforms to a defect due to plastic flow , and that air easily hardens superficially , it being possible to accelerate this process using a gentle airflow from a compressed air pistol . even after 4 hours of centrifuging , no solid or liquid settles out . a large quantity of the material does not result in an aqueous solution settling on the surface , even after standing for a number of weeks . an extruded paste adheres well to surrounding tissue . an extruded and superficially dried body retains its shape in the simulated body environment ( moist chamber under physiological conditions ). 200 mg component e are mixed with 100 mg component a , and then 19 g component c are added while stirring . after a 1 - hour swelling time , the swollen gel is sterile - filtered , slowly added to a total of 58 g component b while stirring , and mixed intimately . the mixture is sterilized in a closed container at 121 ° c . using dry heat . the result is a homogenous mixture that has a plastic consistency and is kneadable , that because of its kneadability is easily applied to a bone defect , that adheres well to the surrounding tissue , and that air easily hardens superficially , it being possible to accelerate this process using a gentle airflow from a compressed air pistol . even after 4 hours of centrifuging , no solid or liquid settles out . a large quantity of the material does not result in an aqueous solution settling on the surface , even after standing for a number of weeks . a hand - formed and superficially dried body retains its shape in the simulated body environment ( moist chamber under physiological conditions ). 500 mg component f are mixed with component c to make 10 . 0 g . after a 4 - hour swelling time , the swollen gel is sterile - filtered , slowly added to a total of 27 g component b while stirring , and mixed intimately . the mixture is sterilized in a closed container at 121 ° c . using dry heat . the result is a homogenous , plastic mass that is kneadable , that because of its kneadability is easily applied to a bone defect , that adheres well to the surrounding tissue , and that air easily hardens superficially , it being possible to accelerate this process using a gentle airflow from a compressed air pistol . even after 4 hours of centrifuging , no solid or liquid settles out . a hand - formed and superficially dried body retains its shape in the simulated body environment ( moist chamber under physiological conditions ). 500 mg component g are mixed with component c to make 10 . 0 g . after a 4 - hour swelling time , the swollen gel is sterile - filtered , slowly added to a total of 22 g component b while stirring , and mixed intimately . the mixture is sterilized in a closed container at 121 ° c . using dry heat . the result is a homogenous , paste - like mixture that is easily extruded through a cannula , conforms to a defect due to plastic flow , and that air easily hardens superficially , it being possible to accelerate this process using a gentle airflow from a compressed air pistol . even after 4 hours of centrifuging , no solid or liquid settles out . an extruded paste adheres well to surrounding tissue . an extruded and superficially dried body retains its shape in the simulated body environment ( moist chamber under physiological conditions ). sterile filtration is performed in 1 . 9 g component h . then 5 g component b are added slowly while stirring . the result is a paste that can flow plastically and that is easily extruded through a syringe . the material can easily flow plastically into the intermediate spaces of a defect . even after multiple hours of centrifuging , the tcp particles remain in suspension . the material is very suitable for a bone construction material , especially for complicated defects . 2 . 0 g component i are mixed with component c to make 10 . 0 g and after homogenization are sterile filtered . after 25 g component b are added the material is mixed intensively . the result is a paste that has good plastic flow and that is easily extruded through a syringe . the material has plastic flow and therefore is ideal for filling intermediate spaces in a defect and adheres to the surrounding tissue . even after multiple hours of centrifuging the tcp particles remain in suspension . the material is very suitable for bone construction material , especially for complex defects . 0 . 2 g component i are mixed with component h to make 10 . 0 g and after homogenization are sterile filtered . after 25 g component b are added the material is mixed intensively . the result is a non - extrudable , kneadable paste that is slightly elastic and is shapeable like wax . because of its shapability , the material can be matched well to different defects and remains in the defect temporarily as a placeholder . even after multiple hours of centrifuging the tcp particles remain in suspension . the material is very suitable for bone construction material , especially for complex defects . 3 . 0 g component k are mixed with component c to make 10 . 0 g . once component k has dissolved , the material is sterile filtered and added to 26 . 3 g component b . the result is a paste that extrudes well through a syringe and that is shapeable and does not drip from the cannula . because of its shapability , the material can be matched well to different defects and remains temporarily in the defect as a placeholder . even after multiple hours of centrifuging the tcp particles remain in suspension . the material is very suitable for bone construction material , especially for minimally - invasive applications . 300 g component d are mixed with component c to make 10 . 0 g . after a 1 - hour swelling time , 25 g component b having the mean grain sizes according to the table below are added and mixed intimately . the result is a paste - like mass , the extrudability of which is tested using different cannula diameters . extrudability is documented in the table below and indicates the suitability of various particle diameters for producing an extrudable paste . + = good to moderate ( satisfactory extrudability , slight resistance can be detected from canting of individual particles ) − = moderate ( adequate extrudability , significant resistance due to canting of particles ) the advantage of the inventive composition is that a phase and sedimentation - stable , plastically deformable implant material with intrinsic pore formation is provided that can be created such that it does not migrate much and is inserted into a bone defect by injection or alternatively can be applied to / fitted in a bone defect as a kneadable mass . in the inventive composition , the liquid or paste components that are soluble in water stabilize the biologically active polygonally broken rounded particles that are difficult to dissolve in water and that are in the size range of 0 . 1 - 150 μm having pores in the size range of 0 . 01 - 50 μm such that they do not convert to other phases or substances due to a dissolution / recrystallization process . moreover , with the inventive application of the paste - like implant material / the inventive composition , the water - soluble organic binder substance with the particulate biologically active substance forms a porous structural accumulation that is dimensionally stable when applied , the easily soluble components being exchanged for fibrous tissue in the defect environment so that the porous particle packing remains dimensionally stable and is slowly integrated , vascularized , and resorbed . all of the features described in the following claims and in the drawings can be essential to the invention , both individually and in any combination with one another .
the invention relates to a phase and sedimentation - stable , plastically deformable preparation with intrinsic pore formation that can be used for instance for filling bone defects and for augmentation , and also relates to a method for producing and using same . the object of the invention , to provide a phase and sedimentation - stable , plastically deformable implant material with intrinsic pore formation , that is not complex to create , and that can be inserted into a bone defect by injection or alternatively can be applied to / fitted in a bone defect as a kneadable mass , is attained in that a plastically deformable preparation for bone construction / replacement based on ceramic suspensions includes a particulate , porous component that is not easily soluble in water and at least one liquid , wax - like , or gel component that is dissolved in water or alcohol , the component that is not easily soluble in water being 60 - 98 % by weight and the component dissolved in water or alcohol being 1 - 30 % by weight , the particles of the particulate component having a diameter in a size range that is essentially greater than a phagocytabler particle and smaller than the passage diameter of standard injection cannulas and the portion of the component soluble in water or alcohol being 0 . 1 - 3 % by weight .