with particular reference to the numerical symbols of the above figures , the intraosseous implantation structure in accordance with this invention designated as a whole by reference number 1 includes a ‘ biomimetic ’ surface which has a particular geometrical conformation consisting of cavities having osteogenetic effect and designated as a whole by reference number 2 . the cavities 2 have a definite characteristic size between 70 and 800 microns with depth variable between 10 and 100 microns . preferably the cavities 2 include micro and macro cavities . the micro - cavities have dimensions between 70 and 200 microns while the macro - cavities are between 200 and 800 microns . these cavities are capable of stimulating within them an intense angiogenetic activity while concentrating the bone growth factors — including bone morphogenetic proteins ( bmp )— to promote bone formation faster compared with the present which takes from 4 to 6 months . in addition , these cavities , once the bone has grown inside them , ensure better and longer stability over the long period to the dental implantation integrated in the bone . as a result from the biomechanical viewpoint there is a considerable increase in the contact surface with the bone and consequently better distribution of the masticatory forces between the implantation and the bone . from the biological viewpoint the cavities are decisive in promoting the formation of the bone faster than now . the implantation structure in accordance with this invention and especially the associated manufacturing method as explained below also allow realizing a custom - made implantation manufactured article for the patient starting from the performance of a tac and its graphic refashioning and obtaining the three - dimensional model of the maxillaries . the implantation can be realized in a single piece fitted with the stump ( not shown in the figure ) already pre - angled to correct any disparallelisms between multiple implantations and / or natural dental elements . in cases where it is wished to proceed to immediate loading of the implantation after its insertion in the bone , on the manufactured article implanting in a single piece and with customized dimensions based on the bone morphology of the individual patient , a ceramic false set of teeth can be constructed in ceramic , resin or metal and ceramic ( not shown in the figure ). obtaining the two above characteristics , implantation and stump in a single customized piece and preconstructed false set of teeth , can take place by using an innovative manufacturing method calling for realization of both the dental implantation and the false set of teeth by sintering of titanium or ceramic powders using a laser beam . it is understood that the manufacturing method can also be used for formation of the implantation without stump or preconstructed prosthesis . as shown diagrammatically in fig4 the implantation 1 can be realized using a productive unit 11 including a controlled - atmosphere chamber 12 in which the article is formed . the powder is deposited in layers ( fig4 shows the just deposited last layer 18 ) on a vertically movable platform 14 along a cylinder 19 . each time a layer of powder is deposited a laser device striker arm 13 generates a sintering laser beam directed towards the layer of powder just deposited so as to form a layer of the implantation . grains of powder struck by the laser melt and immediately afterward solidify again to form part of the implantation . the platform 14 is moved downward by known movement means not shown in the figure as the article is formed . the laser beam is controlled so as to form the cavities 2 having osteogenetic effect on the outer surface of the implantation . the laser device 13 is controlled for this purpose by known control means 15 which can include a pc , where a three - dimensional model of the implantation which it is desired to realize is memorized and an appropriate controller capable of piloting the laser device 13 as a function of the data supplied by the pc on the model of the article . fig4 shows part of the implantation during realization with reference 16 while 17 designates the powder which is not molten by the laser and which can be recovered for a subsequent manufacturing process . the layers deposited can have advantageously a thickness between 1 and 100 microns . the powder used in the process is a metal powder advantageously pure titanium powder or of grade 2 , 4 medical or ceramic titanium . the grains of titanium powder can have nanometric dimensions . preferably as shown in fig4 the layers of powder to be sintered are deposited in accordance with planes perpendicular to the extension of the implantation which has a generally elongated cylindrical or conical form . during the manufacturing process advantageously in the chamber 12 there is an inert gas ( for example argon ) so as to reduced to the minimum the chance that impurities might adhere to the surface of the implantation . it was surprisingly found that the use of laser sintering in the manufacturing process allows obtaining a surface porosity of the implantation with exceptionally good osteointegration properties and quite drastic reduction in the time necessary for healing . in addition , the manufacturing method in accordance with this invention allows obtaining a nearly decontaminated product directly . indeed , when using known manufacturing techniques , the implantations have to then be subjected to costly and laborious decontamination processes aimed at cleaning the article of sandblasting residues , mechanical processing oils or other impurities as necessary . by realizing the implantation using a sintering beam in controlled atmosphere the surface of the article already has a high level of cleanliness . the product , at the most , can be subjected to a mere ultrasound treatment with distilled water or organic acids . connection between the stump and the implantation where construction of the two parts is planned , separate stump and implantation , it is preferably of the pure conical type . fastening of the stump ( not shown ) to the bone screw 1 is obtained by insertion of a shank thereof conformed in accordance with a morse cone inside an axial cavity 4 with a corresponding conformation realized inside the bone screw . this cavity 4 has a troncoconical conformation with tapering toward the tip , or cylindrical . in this cavity the shank of the stump can by coupled by pressure for anchoring of the prosthesis . the stump , however , could also be applied by screwing to the implantation . the cavity 4 is characterized by having a hexagonal shape on the apical bottom 3 where the most spinal part and with the same shape as the stump is engaged . the shape of the bottom of the cavity 4 could however be triangular , square or octagonal . a variant of the bottom form of the cavity 4 of the implantation is to adopt a 5 or 6 - point star design where the shank of the interchangeable stump of analogous form fits . the conical connection allows better mechanical stability , that is a better resistance to masticatory load forces . this connection also allows better biological stability and prevents passage of fluids and bacteria towards the inner parts of the implantation . in addition , the end hexagon or the 5 or 6 - point star ensure correct positioning of the stump by also opposing rotational forces . to allow screwing or positioning of the implantation in the bone , the driver , which bears the implantation , is advantageously provided with an interfaceable hexagon or 6 - point star portion which fits into the most apical part of the inner cavity of the hex - shaped implantation thus making possible application of the necessary force for positioning of the implantation in the bone . as shown in fig1 and 3 , on the outer side surface of the implantation 1 a fraenum is formed which might involve about two - thirds of the length of the implantation . the third apical of the implantation can be solid and its outer surface have the macro cavity of a diameter or 70 to 800 microns . with the new sintering procedure it is possible to construct this part so that all the cavities are interconnected by micropores to constitute a network of intercommunicating cavities and pores allowing colonization by the bone . the surface of the coronal top two - thirds of the implantation has micro cavities 70 to 200 microns in diameter . the top edge at the neck level of the implantation is beveled and smooth with an angulation between 0 ° and 40 °. it is noted that the interconnection micropores between the cavities could be formed at any point of the implantation 1 where there are cavities 2 . it is now clear that the preset purposes have been achieved . an intraosseous implantation structure characterized by having a surface with micro and macro cavities of definite sizes which induce formation of the bone is realized . it is this geometric drawing of the surface which produces the osteogenetic effect . the manufacturing method in accordance with this invention allows realizing a surface porosity provided with micro - cavities such as to lead to surprising and unexpected results form the osteointegration viewpoint . in addition , thanks to the method in accordance with this invention it is possible to exclude from the manufacturing process the laborious and costly decontamination treatments to which the implantations realized using known techniques had to be subjected . naturally the above description of an embodiment applying the innovative principles of this invention is given by way of non - limiting example of said principles within the scope of the exclusive right claimed here . the intraosseous implantation structure in accordance with this invention can be realized to measure in a single piece with form , size and preangulations of the stump so as to allow customized adaptation to the requirements of the osseous formation of the individual patient . the structure is also characterized by a conical joint connection between the stump and the implantation . naturally the materials used as well as and the dimensions can be any , depending on requirements and the state of the art .
a method for making an intraosseous dental implantations including the steps of supplying a layer of powder of a material designed to form the implantation and applying a laser sintering beam to said powder to form a layer of the implantation and repeating the two above operations several times by depositing each time a following layer of powder over the preceding one treated with the laser beam to form the implantation with the laser beam being applied to the powder layers so as to form cavities on a surface of the implantation designed to be colonized by the patient &# 39 ; s bone .