KR101942620B1 - Zirconia ceramic dental implants fused with bioactive glass ceramic artificial bone powders - Google Patents

Abstract

The present invention provides a zirconia ceramic dental implant fused with a bioactive glass ceramic artificial bone powder and a method for manufacturing the same. The dental implant utilizes a non-buried structure, wherein the implant and abutment are integral, the abutment having an abutment rod on the abutment rod, an abutment file on the lower part thereof, And an expandable abutment plate between the abutment files. When the dental implant is an anterior dental implant, the gingival portion of the abutment file has an additional bamboo joint pile joint. When a screw is provided in the implant body and the implant root, the implant body has a shallower trapezoidal screw; The root of the implant has a deeper triangular screw, and the bioactive glass ceramic artificial bone fragments are fused to the area below the implant neck, and the part is implanted into the alveolar bone. The dental implants of the present invention have a moderate structural design, are difficult to break, have biocompatibility better than the biocompatibility of pure titanium implants, and have a greater osseointegration strength than that of hydroxyapatite-coated implants It is a biomedical implant to hold.

Description

TECHNICAL FIELD [0001] The present invention relates to a zirconia ceramic dental implant and a dental implant. [0002] Zirconia ceramic dental implants,

The present invention relates to an artificial dental implant that is fused with a non-metal, zirconia pre-ceramic artificial dental implant, particularly a bioactive glass ceramic artificial bone material that does not damage the surface of a zirconia ceramic, belonging to the technical field of dental medical devices.

For the past 30 years, titanium implants have dominated the field of dental implants, but the metallic color of titanium implants can be visually perceived through thinner gums, thus affecting the appearance and also affecting CT and NMRI (Nuclear Magnetic Resonance Imaging (Nuclear Magnetic Resonance Imaging). Another problem that can not be ignored is that, according to foreign oral medical reports, titanium particles are found to accumulate in the lymphatic glands around the titanium implants, possibly as a source of sensitization. Moreover, titanium is easily oxidized; Under the National Natural Science Fund Project 31200756, in collaboration with the science and technology planning project J12K54 and the Nanjing University of Medicine, Shandong Province high-level institutions, animal experiments of TiO ₂ -Nps were carried out and the results showed that titanium oxide nanoparticles The activity of bone cells is slowed down, stimulates the oxidative stress response of the cells, and at the same time induces apoptosis. Thus, the mechanism of toxic reaction of bone cells induced by TiO ₂ -Nps is the safe application of titanium implants in the transplantation field. And to provide a theoretical basis for this. Funding Project B2011036 of Guangdong Province's Medical Science Research Fund Project, co-research by Oral Medicine of Guangdong Province Oral Medicine, Oral Medicine of Southern Medical University, and Oral Medicine of Nanjing Medical College, "the effect of titanium particles on the osseointegration function of osteoclasts According to another study of " The Influence of the Titanium Particles on the Absorption Function of Osteoclastic Bones ", the results show that titanium particles increase the absorption activity of the osteoclast bone around the implant, which inevitably leads to an additional absorption of scrotalin around the implant And the bones around the implants dissolved, further impairing the stability of the implants. Thus, persons who have high aesthetic expectations and those who require high biocompatibility of implant materials will choose metal-free implants of bioactive materials to be used for dental implantation.

Currently, the best ceramic material implants are zirconia ceramic implants. According to a comparison between zirconia ceramic implants and pure titanium implants via animal implantation experiments performed by foreign researchers Depprich and Park et al., Electron microscopic observations were made: within one week after implantation, the collagen hatch bone matrix was in close contact with zirconia ceramic implants Whereas the collagen hull bone matrix was attached only to the surface cavities of pure titanium implants; Within four weeks of implantation, the BTQ (removal torque) of the BIC (bone-implant-contact) and zirconia ceramic implants between the zirconia ceramic implant and the bone is significantly higher than the BIC and BTQ of the pure titanium implant. In accordance with other studies conducted by the Oral Medicine Institute of Xianyang University of Medicine (710004), in vitro cultured osteoblasts and zirconia have excellent biocompatibility, but are not biologically compatible with any biological activity, bone induction, bone conduction, While the biological activity of pure zirconia acting as an implant material is not sufficiently good and the structure of CaOP ₂ O ₅ should be introduced. In Chinese patent document CN201110326532.0, " Surface Treatment of Zirconia Implants " belongs to this type of implant that does not include the CaOP ₂ O ₅ structure bonded with bone chemical bond, and the bonding strength with bone structure May be improved only by fabricating porous structures on surfaces with low activity.

The fatal weaknesses of ceramics are high vulnerability and low reliability, and dental implants manufactured by zirconia ceramics are often broken in anterior dental implants with small diameters, or in threaded portions of implants; On the other hand, defective points caused by any surface treatment of the acid-etched sand blast on the implant as well as the surface micro-pores can cause breakage. Titanium implants can also be fractured and there is a weakness in the anterior dental implant with a smaller diameter or in the central threaded location of the internal connection, some are broken within a year, and some are broken after several years. Nowadays, many countries have considered the problems of fracture of titanium implants, and their solutions are as follows: Thick neck and dental implants with small diameters are made of integral dental implants, ie abutments It is integrated with the implant. Thus, zirconia ceramic implants can also be improved in their structure for titanium implants to prevent breakage. Chinese patent CN200410029886.9 discloses that ceramics having high tensile fracture toughness of up to 15 to 17 MPa · m ^1/2 can be obtained through aluminum hydroxide coated on the outside of nano-zirconia powders and pressureless sintering; The cell culture in which aluminum is added by the aluminum contained therein contains a high content of aluminum in the bone tissue which reduces osteoblasts, inhibits bone regeneration, and causes osteomalacia of bone; Similarly adding a small amount of aluminum into pure titanium can also increase the strength of titanium, which can not be used in implants by the aluminum elements contained therein, and can be used by international organizations for standardization (ISO 6474-2) There is an experiment of implanted hips made with zirconia-reinforced high purity aluminum oxide performed, which may not be applied to bone grafting because the hip joint does not require bone ingrowth and rigid bonding with bone tissue. Under the cooperation of the Guangzhou Association of Advanced Technology of the Chinese Academy of Sciences and the Department of Oral Medicine of Xiaoshan University, according to the National Natural Science Fund Project 61204325, "a three-dimensional finite element between the stress distributions of dental implants and surrounding bone tissues Comparison "shows that the effect of the screw on the implant is not obvious, the stress on the interface between the straight abutment and the non-buried implant is minimal, and the straight abutment and the non-buried implant constitute the optimal combination. Thus, we choose an integrated dental implant, where the implants and abutments are integral. In the past, some doctors believed that the various screws of the implants were patented because they were misled by the seller's advertisement. Creator bone resorption caused by inflammation around the implants due to poor oral hygiene was induced by non-implantable implants, and all these misunderstandings were actually true, and when the non-implantable implants were implanted, When the post-implant hygiene has deteriorated, the implanted implants also cause peri-implantation and bone resorption. In fact, the connection between the center connection hole and the abutment of the thinner neck of the anterior portion of the two-piece anterior dental implant requires the highest machining accuracy, the most difficult to handle and the position is also affected by the breakage of the implant, It is a place where bone absorption is very likely to occur. Another patent document CN20091004273.0, " Zirconia Dental Implant " discloses a technical solution of a two-piece dental implant fused with a hydroxyapatite (HA) coating, in which a two-piece dental implant is connected, , Whose structure is treated with a zirconia powder block or a zirconia ceramic rod, the material has high hardness and fragility and is particularly suitable for processing female threads of the internal bore of the implant to engage with the male thread of the abutment , High precision is required and the pieces are difficult to handle due to their high hardness and fragility, so that the pieces are rarely used in clinics. For dental implants having a surface fused with a layer of hydroxyapatite artificial bone meal, the fracture toughness is only 0.7 to 1.3 MPa · m ^1/2 by the low strength of the hydroxyapatite; When hydroxyapatite is directly produced through hydrothermal synthesis and fused directly to the zirconia ceramic body, hydroxyapatite is easily absorbed away and its rate of degradation is difficult to match with growth of body tissue; When the hydroxyapatite is fused or sprayed directly onto the zirconia ceramic body, both have a melting point of at least 1650 DEG C, and when the temperature reaches 1200 DEG C, the hydroxyapatite burns the hydroxyl group and becomes an inactive oxyapatite, Plasma spraying does not work, and WestChina Oral Medical College has stopped using implants that have been fused with HA since 20 years ago, so hydroxyapatite has rarely been used clinically.

There are also dental implants made of hydroxyapatite / ceramic composites that improve strength and adhesion but have reduced biological activity and biocompatibility and are complex to manufacture; Patent document CN200710045510.0, "Method for manufacturing situ of nano-zirconia / hydroxyapatite composite powder" belongs to this type. The present invention relates to a process for the preparation of hydroxyapatite which possesses excellent biocompatibility and can be bonded to the chemical bond of bone tissue and which may not contain any constituents harmful to the human body and which possesses a higher mechanical strength than the mechanical strength of the hydroxyapatite and which is not easily absorbed (BGC). ≪ / RTI > 12th for the national institution by the Ministry of Health According to the content recorded on page 229 of the 5-year planning manual, " Dental Materials Science ", the bioactive glass ceramic has a bending strength of 180 to 200 MPa and a fracture toughness of 2 to 2.5 MPa · m ^1/2 ; The bioactive glass ceramic implanted into the bone facilitates bone formation and facilitates bone repair to form a bonded chemical bond and the new bone can be seen on the surface of the material within 10 days after implantation, Have formed strong bonds within 60 days of implantation, so that the bond strength to bone is 20% higher than that of hydroxyapatite within 8 weeks of implantation. The study of bioactive glass ceramics has a long history in China and the evaluation meeting was organized by the Sichuan Provincial Party Committee already held on September 18, 1986 by Hanzhang WANG, the dean of the West China University of Medicine, The bioactive glass ceramic artificial bone material developed by the Institute of Optics and Electronics has achieved international progressive levels. Animal experiments have demonstrated that in the samples of bioactive glass ceramics implanted into dog jaws for 6 months, new bone and hibernate formation can be seen in the particles and new bones grow into the particles. According to the National Natural Science Fund Project 50830101, the Department of Oral Medicine at Peking University conducted a study of the function of bioactive glasses on vascular growth factors of human pulp cells, and the results show that bioactive glass ceramics Can promote the proliferation of gene expression and the secretion of vascular endothelial growth factor (VEGF) and basic fibroblast growth factor (BFGF). Another study, "Effects of Micro / Nano Surface Implants on Implant Osteosynthetic Spheres," was conducted by the National Science Foundation Fund Project 30900284, 31100668, and Shaanxi University Subject 200K-03-01, , And the Department of Oral Medicine of Jilin University, and the result is that the micro / nano surface significantly stimulates the innate bone structure, which can significantly improve the healing rate at the bone-implant interface . These conclusions provide theoretical reasons for clinical practice.

In order to fuse the bioactive glass ceramic powder to the surface of the zirconia ceramic, a bonding ceramic having a low melting point and an expansion coefficient similar to the low melting point and expansion coefficient of zirconia is used. The bonding ceramic has a thermal expansion coefficient of 10.2 K and a thermal expansion coefficient of 2.75 Mpa m < ^{1/2 &} gt ;. Ivoclar Vivadent Nano-Apatite Glass Ceramic IPS With the zirconia-specific bonding ceramic powder of the e.max system, micro- and nano-bioactive glass ceramic powders can be fused onto the zirconia surface through cleaning. Another type of elastic ceramic produced by the German VITA company, VITA ENAMLC, has elastic modulus substantially similar to the elastic modulus of a congenital tooth, and is preferably capable of reducing impact on the implant and reducing crater type absorption It acts as a dental crown.

Currently, zirconia has been applied industrially and commercially in the process of making dental powder blocks and sintering all ceramic crowns, but zirconia has not yet been successfully applied in the field of implants. By a complex ceramic enhanced process 6Mpa · m ^1/2 to The fracture toughness of the reinforced zirconia ceramics improved to 12 Mpa · m ^1/2 was continuously improved and the laboratory study exceeded 15 Mpa · m ^1/2 (Maski) and even reached to 20 Mpa · m ^1/2 However, this level can usually be reached in practical applications. A certain amount of adhesive such as polyvinyl alcohol, paraffin and the like is banburyed and milled by the supplier and then added into yttria stabilized zirconia ceramic (Y-TZP) powder, and the block materials are injection molded Or pre-sintering (1000-1200 ° C), and sent to the Department of Dentistry for machining the shape by CAD / CAM with computer numerical control equipment followed by product molding through sintering at 1520 ° C. Due to the well-known stiffness-induced deformation enhancement, zirconia has a cubic state c-ZrO ₂ To tetragonal t-ZrO ₂ followed by monoclinic phase m-ZrO ₂ , the phase transformation is reversible at 1170 ° C and a volume change of 3% to 5% occurs, which is called martensitic Phase transformation is enhanced, and the time and temperature of the phase transformation must be ensured. Although the phase transformation is reversible, the effect is not good when the temperature is higher than 1200 deg. To meet the transparency and beauty requirements of the clinical crown, the supplier should adjust the dose of stabilizer yttrium Y ₂ O ₃ , Which will result in a reduction in the strength of the ceramics and no nano-zirconia-specific stress-induced transformation enhancement may be present, for example the disclosures of the patent documents US20070375001 and CN102023624B belong to transparent zirconia.

A foreign researcher, Tsukuma et al., Used CeO ₂ stabilized zirconia ceramic Ce-TZP sintered at room temperature followed by sintering by hot isostatic pressing (HIP) at a temperature of 1500 ° C. and a pressure of 200 MPa for 2 hours. The fracture toughness was 30 MPa · M ^1/2 could be reached, but HIP equipment is too expensive, has high technical requirements, and, furthermore, the color of Ce-TZP is not good enough. Products that require too expensive equipment and that have too high technical requirements may not be adopted for private use, and thus only Y-TZP treated with pressureless sintering can be used , And the sintering method is as follows: (1) warm to 1 ° C per minute; (2) the temperature range of 950 DEG C to 1150 DEG C is in the phase sensitive range, while the temperature is raised slowly for 6 hours. Ceramic strengthening is a complicated process, and it is not so easy to increase the toughness of the zirconia to 6Mpa 占^{1/2 1/2} to 15Mpa 占 퐉 ^1/2 or more (the toughness of the ceramic is increased more than twice); When the temperature is in the range of 100 占 폚 to 300 占 폚, the unstable state transition occurs in the Y-TZP where the strength decreases and the strength is reduced, so that the treatment must be realized with water cooling, And the actual fracture toughness should be measured after the product is produced. As an example, the stress on the anterior teeth is 1.5 Mpa, the fracture toughness should be 12 Mpa · m ^1/2 when the diameter of the gingival portion (implant neck) is 4 mm, and the fracture toughness · 15Mpa be implants with a diameter of φ3.5mm only be achieved m ^1/2 or more production and the low reliability of the zirconia ceramic should also be considered. In clinical practice, the molars are subjected to a maximum stress of 6 Mpa, which is a normal stress, and a 1.5 Mpa stress is applied to the anterior forebears from the pure-palatal side, lateral and bending forces. The clinician's solution is as follows: (1) implants with larger diameters are implanted by separating the alveolar bone of the anterior teeth, separating the bone, (2) adjusting the stress angle when the angle of the implant is too large To separate the bones in the direction; (3) Adjust the jaws to prevent the implants from coming into intimate contact with other teeth. (4) Patients are prohibited from eating some foods that are too difficult to protect teeth.

It is an object of the present invention to provide a metal-free dental implant that has a suitable structural design and is difficult to break down. The dental implant has a section that fuses with the bioactive glass ceramic artificial bone fragments and the portion is implanted in the alveolar bone, the dental implant is hard to break, and the biocompatibility of the pure titanium implant is better than the biocompatibility ≪ / RTI > and are biomedical implants that are more active and have higher osseointegration strength than hydroxyapatite-coated implants.

A particular technical configuration of the present invention is as follows:

A dental implant for zirconia ceramics fused with a bioactive glass ceramic artificial bone meal including an implant and an abutment, wherein the dental implant is an anterior dental implant and has a diameter of? 4.0mm to? 4.5mm and has a non- Wherein the implant and abutment are integral, the abutment having an abutment load on its upper portion, an abutment load on its lower portion, and an abutment load between the abutment load and the abutment file, Wherein the abutment file has a diameter of 4 mm or more and the transgingival part of the abutment file has an expanded bamboo-joint type file joint, so that the abutment file can be easily And a screw is provided on the implant body and the root of the implant , The implant body has a shallower trapezoidal screw, the implant root has a deeper triangular screw, and the bioactive glass ceramic artificial bone fragments are fused to the area below the implant neck, and the part is implanted into the alveolar bone.

A zirconia ceramic dental implant fused with bioactive glass ceramic artificial bone fragments comprising an implant (1a) and an abutment, wherein the dental implant is a posterior dental implant and has a diameter of 5 mm Wherein the implant and the abutment are integral and the abutment has an abutment rod on top thereof, an abutment file on the underside thereof, and an abutment rod and abutment Wherein the abutment file has a diameter that is slightly less than the diameter of the implant but greater than 4 mm, and wherein the implant body and the implant root are provided with a thread, the implant body With shallower trapezoidal threads, and the implant root has a deeper triangular screw Wherein a tail cut groove is disposed on the screw of the implant root and the bioactive glass ceramic artificial bone fragments are fused in the region below the implant neck and the region is implanted in the alveolar bone.

In the anterior implant dental implant and posterior dental implant, the abutment rod of the abutment has a taper angle of 1.5 degrees and a length of 5 mm to 7 mm, and the abutment file has a length of 3 mm to 4 mm.

In the anterior implants and posterior dental implants, zirconia ceramic dental implants were prepared from 3 mol% Y ₂ O ₃ stabilized tetragonal zirconia polycrystalline (3Y-TZP) reinforced by stress-induced phase transformation, Ceramic.

In the anterior implants and posterior dental implants, a mixture of micro and nano bioactive glass ceramic artificial bone fragments is used as bioactive glass ceramic artificial bone fragments.

A manufacturing method for a zirconia ceramic dental implant of the present invention comprises the following procedure:

1) Raw material preparation step: Nano 3Y-TZP powder is taken as the main raw material, then the organic vehicle, polyethylene and paraffin are added after being banburyed and fully ground, and the block material or bar materials are added at 300 MPa And then the organic beak is removed by slow pre-sintering, and the raw material is ready for use;

2) Blank manufacturing step: Zirconia implant blank cores are obtained through processing by CAD / CAM equipped with computer numerical control equipment.

3) Phase Transformation Strengthening and Sintering Step: Computer numerical control for pressureless sintering A zirconia implant blank core is placed in a sintering furnace, the temperature is increased by 1 ° C per minute and sintered stepwise, where the temperature range from 950 ° C to 1150 ° C Is in the phase sensitive range, during which the temperature is raised or lowered by 0.5 [deg.] C per minute; A zirconia ceramic implant reinforced by phase transformation is obtained after sintering.

4) Fusing step with bioactive glass ceramic artificial bone meal: Spraying one layer of an organic viscous aqueous solution onto a portion of a zirconia ceramic implant by a rotating table and ultrasonic, this part should be implanted into the alveolar bone, and the Ivoclar Vivadent nano- The IPS further sprayed one layer of the zirconia-specific bonding ceramic powder of the MAX system, said layer having a thickness of 0.02 mm to 0.04 mm, fused to the surface of the zirconia ceramic implant sintered at 750 占 폚, Forming a bonded porcelain layer and, additionally, a layer of micro- and nano-bio-active glass ceramic powder is sprayed onto the surface of the magnetic layer bonded by the same method as above, , And in this way, the bioactive glass ceramic artificial bone particles are bonded Is fused onto the zirconia ceramic implant through the base layer.

The dental implant of the present invention has the following advantages: Biocompatible glass ceramic artificial bone fragments that have a suitable structural design, are difficult to separate, and are fused in a session to be implanted in the alveolar bone, Has better biocompatibility than zirconia implant biocompatibility and possesses higher osseointegration strength than osseointegration strength of hydroxyapatite-coated implants.

1 is a schematic structural view of an anterior dental implant according to the present invention.
2 is a schematic structural view of a posterior dental implant according to the present invention.
FIG. 3 is a schematic structural view of a two-piece dental implant according to the present invention, wherein the implant is embedded in bone.
4 is a schematic structural view of a two-piece dental implant according to the present invention, wherein the implant is embedded in the gum.
5 is a straight plug-in style abutment of a two-piece implant.
Figure 6 is a bent plug-in abutment of a two-piece implant.
In Figure 1: 1 - Implant, 1.1 - Implant neck, 1.2 - Implant body, 1.3 - Implant root, 2 - Abutment, 2.1 - Abutment load, 2.2 - Abutment plate, 2.3 - Abutment file , 2.4 - abutment file joint, 3 - part fused with bioactive glass ceramic artificial bone meal
In Fig. 2: 1a - Implant, 1.1a - Implant neck, 1.2a - Implant body, 1.3a - Implant root, 1.4a - Tail incision, 2a - Abutment, 2.1a - Abutment rod, 2.2a - abutment plate, 2.3a - abutment file, 3a - the part fused with bioactive glass ceramic artificial bone meal.

The invention is further illustrated by the following description in combination with the accompanying drawings.

Figure 1 shows an anterior dental implant of the present invention comprising an implant 1 and an abutment 2, wherein the anterior dental implant has a diameter of from 4.0 to 4.5 mm using a non- It is a thin implant. The implant 1 and the abutment 2 are integrated and the abutment 2 has an abutment rod 2.1 on the abutment and an abutment file 2.3 below the abutment, And includes an expandable abutment plate (2.2) between the budget rod (2.1) and the abutment file (2.3). The abutment rod 2.1 has a length of 5 mm to 7 mm and a taper angle of 1.5 degrees to plug-in and fix the detal crown. The anterior implant dental prosthesis has a diameter of 4 mm or more and the abutment file 2.3 of the abutment 2 has a solid diameter of 4 mm or more to prevent brittle fracture. Furthermore, in order to increase the strength of the abutment file 2.3, the gingival portion of the abutment file 2.3 reduces the length of the thinner portion of the abutment file 2.3, increases the diameter of the joint, Further comprising an extended bamboo joint file joint (2.4) for moving the bamboo joint file joint (2); Moreover, pile joints can replace the general implant platform and prevent bacteria from entering the implant from the treatment incision. The implant neck 1.1 does not have any screws to prevent breakage. The implant body 1.2 and the implant root 1.3 are provided with screws and the implant body 1.2 has a shallower trapezoidal screw to prevent the implant body 1.2 from breaking; The implant root (1.3) has a deeper triangular screw to facilitate implantation of the implant root (1.3). To increase the biocompatibility of the implant, and to accelerate osseointegration, the bioactive glass ceramic artificial bone fragments are fused to the lower part of the implant neck, which is implanted in the alveolar bone.

FIG. 2 shows the posterior dental implant of the present invention. The posterior dental implant is a thick implant having a diameter of? 5 mm to? 6 mm, and also uses a non-buried structure such as the structure of an anterior dental implant. The implant 1a and the abutment 2a are integrally formed and the abutment 2a has an abutment rod 2.1a on the abutment, an abutment file 2.3a on the abutment bottom, And includes an expandable abutment plate 2.2a between the abutment rod 2.1a and the abutment file 2.3a. The abutment rod 2.1a has the same taper angle as the angle of the anterior implant. Posterior dental implants are thicker than anterior dental implants and can withstand greater occlusal forces and shear forces so that abutment piles 2.3a are slightly smaller than the diameter of the implant but larger in diameter than 4mm, The marginal bone resorption of the supporting implant can be controlled and the implant is not easily broken and therefore it is necessary to mount the abutment file 2.3a with the abutment file joint 2.4a with the anterior dental implant It is different in that it does not exist. The implant body 1.2a and the implant root portion 1.3a are provided with screws, the implant body 1.2a has a shallower trapezoidal thread, the implant root portion 1.3a has a deeper triangular screw, And the tail cutting groove 1.4a are disposed on the screw of the implant root portion 1.3a. In addition, the bioactive glass ceramic artificial bone fragments are fused at the lower part of the implant neck portion 1.1a, and this portion is implanted into the alveolar bone.

In the anterior and posterior dental implants, a zirconia ceramic dental implant is reinforced by stress-induced phase transformation and consists of a stable tetragonal zirconia polycrystalline (3Y-TZP) ceramic 3 mol% Y ₂ O ₃ , when the deformation of the gum portion of the implant diameter φ4mm, 12MPa · m ^1/2 than to 3Y-TZP ceramic is used having a high fracture toughness. A mixture of micro- and nano-bioactive glass ceramic artificial bone fragments is fused to the lower part of the implant neck and the part is implanted into the alveolar bone.

In the present invention, one-piece implants can be replaced by two-piece implants to accommodate the surgeon's habits of some doctors. Figures 3 and 4 illustrate a schematic structural view of a two-piece dental implant according to the invention, wherein the implant is embedded in the bone and embedded in the gum, respectively, and the corresponding straight plug-in abutment or angled plug- The abutment is shown in Figures 5 and 6. Implants embedded in the bone with screws in the neck of the implant have a diameter of at least 5.5 mm, and implants embedded in the gum in the neck of the implant have a diameter of at least 5 mm. Preferably, such an implant has a diameter of 15 MPa · m than ^1/2 is made of a zirconia ceramic rod having a high fracture toughness. The abutment file that matches the implant of the two-piece dental implant should have an appropriate size and the abutment file may engage a two-piece dental implant by plug-in and adhesive bonding, and The abutment file has a taper angle in the range of 1.5 DEG to 1.9 DEG or 6 DEG to 8 DEG.

A manufacturing method for a zirconia ceramic dental implant includes the following steps:

1) Step of preparing the raw material: The nano 3Y-TZP powder is taken as the main raw material, then the organic beaks such as polyethylene and paraffin are banburyed, sufficiently grinded and added, uniformly dispersed to remove the aggregate, And a high density block material or bar material are obtained under 300 MPa crustal equilibrium pressure, and then the organic beak is removed by slow pre-sintering, and the stock is ready for use.

2) Step of producing a blank: The center of the zirconia implant blank is obtained by processing by CAD / CAM equipped with computer numerical control equipment.

3) Phase Transformation Strengthening and Sintering Step: The center of the zirconia implant blank is placed into a computer numerically controlled sintering furnace for pressureless sintering, the temperature is raised by 1 ° C per minute, and sintering occurs stepwise, The temperature is a phase sensitive range during which the temperature is raised or lowered by 0.5 ° C per minute. The sintering process is specified as follows: the temperature is raised by 1 DEG C per minute from ambient temperature to 300 DEG C by heating, and the temperature is maintained for 3 hours, then the temperature is increased by 1 DEG C per minute to 950 DEG C , And maintaining the temperature for 3 hours, further increasing the temperature by 0.5 占 폚 per minute to 1150 占 폚 and maintaining the temperature for 3 hours, and further increasing the temperature by 1 占 폚 per minute to 1520 占 폚 , And maintaining the temperature for 3 hours, then continuously lowering the temperature by 1 占 폚 per minute to 950 占 폚, and maintaining the temperature for 3 hours, finally lowering the temperature to room temperature continuously by 2 占 폚 The steps are specified. A zirconia ceramic implant reinforced by phase transformation is obtained after sintering.

4) Fusing with bioactive glass ceramic artificial bone fragments: Spraying one layer of an organic viscous aqueous solution onto a portion of a zirconia ceramic implant by a rotating table and ultrasonic waves, the portion being implanted into alveolar bone; Spraying one layer of the Ivoclar Vivadent nano-apatite glass ceramic IPS monolithic glazing-specific bonding ceramic powder, said layer having a thickness of 0.02 mm to 0.04 mm, and sintering at 750 < 0 & Forming a bonded magnetic layer that is fused on the surface of the implant. Additionally, one layer of the mixture of micro- and nano-bioactive glass ceramic powders is sprayed onto the surface of the magnetic layer bonded by the same method as described above, sintered and fused in this manner at 650 DEG C to 700 DEG C, The active glass ceramic artificial bone fragments are fused onto a zirconia ceramic implant through a bonded magnetic layer. The temperature is raised or lowered by 2 [deg.] C per minute during the process of fusing and sintering the bonded magnetic layer and the bioactive glass ceramic artificial bone meal layer.

The implants of the present invention are primarily used for cosmetic implants and metal-free biocompatible implants. In order to begin dental implantation, the patient's needs for cosmetics should be understood; Prior to surgery, CBCT (cone-beam CT) irradiation is performed and an implant guide should be made to sinter the implant to allow the patient to see the entire process of the dummy implant and prosthesis, and any inflammatory or adjacent tooth problems If so, these problems should be solved before surgery. A detailed embodiment is provided as follows.

As an example, an implant is formed within only three months after the middle tooth has been extracted, and an all-in-one implant with a dimension of? 4 x 25 mm is employed.

1) performing the CBCT examination of the patient, then using the corresponding software according to the 3D image obtained to form the dummy implant, then using the electronic file to obtain the results, the physician's advice, To a department or a factory; A step of making a zirconia ceramic artificial tooth fused with an implant guide, a resin tooth used for a restoration treatment, and a biological ceramic by a plant part or a prosthetic part; Performing the surgery when everything is in place. Here, the physician should have a wealth of clinical knowledge.

2) performing local anesthesia with lidocaine, adjusting to the surgical guide, and stepping through the holes with the guidance of the drill needle; If the alveolar bone is not wide enough, the alveolar bone can be pierced after the alveolar bone has been flattened, the alveolar bone can be pierced, the alveolar bone can be divided and widened and occasionally the alveolar bone needs to be divided in the direction, It is necessary to fix it with a screw. Screwing the implant into an implant hole having a torque of 35 Ncm to 45 Ncm; implanting the entire portion of the implant neck into the alveolar bone, the portion fusing with the bioactive glass ceramic; expanding the abutment file inside the gum; Shaped joint file joint so that the abutment file joint replaces the implant platform and prevents the abutment file from being detached in the future; Forming an essentially inducible shape in the soft tissue for the prosthesis, and immediately installing a resin crown; A step of adjusting the jaw, a step of applying a deformation force to the implant, and a step of temporarily fixing the implant to the adjacent tooth by a Maryland bridge.

3) observing intraoperation by the patient; Whenever a patient is not satisfied, transplanting soft tissue or implanting more bone until the patient is finally satisfied.

4) Steps to teach the patient to avoid any food that is too hard after surgery. A step of performing a retest to the patient within one week, one month, or half a year, and replacing the entire ceramic crown of VITA ENAMIC elastic zirconia ceramic within 6 months as follows: Ceramic-specific silicone-based coupling agent Z-prine ^TM Applying Bis-GMA (bisphenol A double methyl acrylate glycyl ester) flow packless photo-curable resin for adhesive bonding, and washing the excess resin with ethyl alcohol to fix the crown Followed by photocuring for 40 seconds. The zirconia ceramic implant is secured to the crown or abutment by a tapered stroke plug-in, fixed by light-curable resin adhesive bonding.

Claims (11)

1. A zirconia ceramic dental implant that is fused with bioactive glass ceramic artificial bone fragments, including an implant (1) and an abutment (2)
Wherein the dental implant is an anterior dental implant and the dental implant is a thin implant having a diameter of? 4.0 mm to? 4.5 mm and using a non-buried structure, the implant (1) and the abutment (2) Wherein the abutment (2) comprises an abutment rod (2.1) on its upper part, an abutment file (2.3) below the abutment rod (2.1) and an abutment file And an expandable abutment plate (2.2) between the abutment plates The abutment file (2.3) has a diameter of 4 mm or more; The transgingival part of the abutment file (2.3) further comprises an extended bamboo-joint type file joint (2.4); The implant body (1.2) and the implant root (1.3) are provided with screws, the implant body (1.2) having a shallower trapezoidal thread; Characterized in that the implant root (1.3) has a deeper triangular screw, and the bioactive glass ceramic artificial bone fragments are fused to the area under the implant neck (1.1), said region being implanted in the alveolar bone.
Dental implants. The method according to claim 1,
The abutment rod 2.1 of the abutment 2 has a taper angle of 1.5 degrees and a length of 5 mm to 7 mm and the abutment file 2.3 has a length of 3 mm to 4 mm As a result,
Dental implants. The method according to claim 1,
Characterized in that the zirconia ceramic dental implant is made of 3Y-TZP ceramics reinforced by stress-induced phase transformation.
Dental implants. The method according to claim 1,
Characterized in that a mixture of micro and nano bioactive glass ceramic artificial bone fractions is used as bioactive glass ceramic artificial bone fragments.
Dental implants. A method of manufacturing an implant according to claim 1, comprising the steps of:
(1) As a raw material production step: Nano 3Y-TZP powder is taken as a main raw material, organic birds, polyethylene and paraffin are then banburyed and fully ground and added, and block materials or Bar materials are obtained under an equilibrium pressure of 300 MPa and then the organic beaks are removed by slow pre-sintering so that the raw materials are ready for use;
(2) as a blank manufacturing step: zirconia implant blank cores are obtained through processing by CAD / CAM with computer numerical control equipment;
(3) As a phase transformation strengthening and sintering step: a zirconia implant blank core is placed in a computer numerically controlled sintering furnace for pressureless sintering, the temperature is raised by 1 ° C per minute, sintered stepwise, and heated to 950 ° C to 1150 ° C The temperature range is a phase sensitive range, during which the temperature is raised or lowered by 0.5 ° C per minute; Wherein a zirconia ceramic implant reinforced by phase transformation is obtained after sintering;
(4) fusing with bioactive glass ceramic artificial bone fragments; Spraying a layer of an organic viscous aqueous solution onto a portion of the zirconia ceramic implant by means of a rotating table and ultrasonic waves, the portion being implanted in the alveolar bone; One layer of a zirconia-specific bonding ceramic powder of the Ivoclar Vivadent nano-apatite glass ceramic IPS e.max system was further sprayed, and one layer of the zirconia-specific bonding ceramic powder had a thickness of 0.02 mm 0.0 > 0.04mm < / RTI > and sintered at 750 DEG C and fused onto the surface of the zirconia ceramic implant to form a bonded porcelain layer; Additionally, one layer of a mixture of micro- and nano-bio-active glass ceramic powder is sprayed onto the surface of the bonded magnetic layer by the same method as above and sintered and fused at 650 ° C to 700 ° C, Wherein active glass ceramic artificial bone fragments are fused onto the zirconia ceramic implant through the bonded magnetic layer. 6. The method of claim 5,
Wherein the sintering step in the step (3) is specified as follows:
The temperature was raised from room temperature to 300 占 폚 by heating by 1 占 폚 per minute, the temperature was maintained for 3 hours, then the temperature was increased by 1 占 폚 per minute to 950 占 폚, the temperature was maintained for 3 hours, , The temperature is maintained for 3 hours, the temperature is further increased by 1 占 폚 per minute to 1520 占 폚, the temperature is maintained for 3 hours, and then the temperature is increased to 950 占 폚 by 1 占 폚 Steadily lowering the temperature, maintaining the temperature for 3 hours, and finally lowering the temperature continuously to 2 ° C per minute to room temperature. 6. The method of claim 5,
Wherein in step (4), during the process of sintering and fusing the bonded magnetic layer and the bioactive glass ceramic artificial bone meal layer, the temperature is raised or lowered by 2 占 폚 per minute.
delete delete delete delete

Images