• 专利附录
  • 专利说明
  • 权利要求
  • 类似技术
  • 同族专利
  • 引用文献
  • 法律状态
  • 优先权
    • 专利摘要:
    (Problem) To obtain an improved biocompatibility and high bone attachment of an implant body, a manufacturing method for the implant body and a dental implant. (Solution) The implant body (2) is fixed in a contact configuration with a bone, and includes the base material (2a) formed of zirconia and a surface layer (2b) formed on the surface of the base material (2a) and having a lower hardness than the base material (2a) Therefore, in addition to having a superior mechanical strength, due to the strength of the zirconia base material (2a), the soft and flexible surface layer (2b) acts as a buffer layer which mitigates the difference in hardness between the bone and the base material (2a), and thus improves the softness. the surface bone attachment properties further. (FiQ-2)
    公开号:SE1051232A1
    申请号:SE1051232
    申请日:2009-05-29
    公开日:2010-11-24
    发明作者:Teruo Ishiwata
    申请人:Nanto Seimitsu Co Ltd；
    IPC主号:
    专利说明:

    [4] Patent Document 1: Japanese Patent Application Laid-Open No. 4046213.
    [5] (Problems Solved by the Invention) The following problems remain unresolved in the conventional art. In other words, in the technique described in patent document t, even if the biocompatibility is improved by roughening the surface by applying a mechanical process, laser process or the like to the surface of the implant, a roughening is simply not sufficient, and Achieving improved biocompatibility and a high level of leg attachment is difficult. Accordingly, there is a need for an implantation body which is provided with an improved biocompatibility and which enables a strong bone connection, and in particular there is a need for an implantation body formed of a ceramic material which has a superior biocompatibility, mechanical strength and the like. _ i
    [6] The present invention is proposed in the light of the above problems, and has the object of providing an implantation body, a manufacturing method for the same and a dental implant which enables an improved biocompatibility and enables a strong bone attachment.
    [7] (Solving the Problem) The present invention applies the following configuration for the purpose of solving the above-mentioned problems. In other words, the implant body of the present invention is an implant body which is fixed in a contact configuration with the bone, and is characterized in that a configuration of the base material is formed of zirconia, and that the surface layer is formed on the surface of the base material and has lower hardness than the base material. 010 15 20 25 30
    [8] Since the implant body includes the base material formed of zirconia, and the surface layer is formed on the surface of the base material and has a lower hardness than the base material, the soft and flexible surface layer acts as a buffer layer which mitigates the difference in degree of hardness between the bone and the base material. - has a superior mechanical strength due to the base material, and therefore the soft surface further improves the bone adhesion properties. -
    [9] The implant body according to the present invention is characterized by the formation of a plurality of crack cavities in the surface layer.
    [10] In addition, the implant body according to the present invention is characterized in that the hardness of the surface layer is lower than or equal to the hardness of the bone. In other words, since the hardness of the surface layer is lower than or equal to the co-hardness of the bone, attachment of the bone tissue is facilitated by the flexible surface which has the same hardness as the bone or is softer than the bone
    [11] In addition, the surface layer of the implant body according to the present invention is characterized by being formed of zirconium hydroxide. In other words, since the surface layer of the implant body is formed of zirconium hydroxide, good bone adhesion characteristics and improved bone compatibility with bone tissue are obtained through a zirconium hydroxide surface layer. In other words, the zirconium hydroxide surface layer is believed to have an ion exchange function and enhances the increase of calcium ions and cell migration, thereby obtaining a significant improvement in bone adhesion.
    [12] The dental implant of the present invention is characterized in that the implant body of the present invention is provided for insertion into a borehole in the alveolar bone which acts as the bone, and is fixed thereto. This means that since the dental implant is provided with the implant body of the present invention which is inserted and fixed in a borehole in the alveolar bone, a superior mechanical strength is obtained, and a good bone adhesion to the alveolar bone is obtained by the soft flexible surface layer.
    [13] The manufacturing method of the implant body according to the present invention is a manufacturing method of the implant body which is fixed in contact configuration with the bone. The method is characterized by including the step of forming a zirconia hydroxide surface layer having a lower hardness than the base material on the surface of the zirconia base material by irradiating laser light into air including water vapor.
    [14] In other words, in the manufacturing method of the implant body, when the zirconium hydroxide surface layer having a lower hardness than base material is formed on the surface of the base material formed of zirconia by irradiation of I-acerius in air including water vapor, the formation of a soft surface layer of zirconium hydroxide with a high adhesion to the base material surface.
    [15] The manufacturing method of the implant body according to the present invention is characterized in that the laser light is laser light which has a fundamental wave caused by a Nd: YAG laser or a YVO4 laser. In other words, since the manufacturing method of the implant body uses laser light with a ground wave caused by an NdIYAG laser or a YVO4 laser, a zirconia hydroxide surface layer is formed on the surface of the short-wavelength high-energy zirconia base material, and facilitates the image formation.
    [16] The manufacturing method of an implant body according to the present invention is characterized in that the hardness of the surface layer is lower than or equal to the hardness of the bone as a result of the irradiation with the laser light. In other words, since in the manufacturing method of an implant body the hardness of the surface layer is lower than or equal to the hardness of the bone as a result of the irradiation with the laser light, as shown above, a surface layer is obtained which facilitates the attachment of bone tissue. .
    [17] (Effect of the Invention) The present invention achieves the following effect. In other words, since the implant body of the present invention and the manufacturing method 1 therefore form a surface layer which has a lower hardness than the base material on the surface of the zirconia-formed base material, in addition to having a mechanical strength exceeding the zirconia-dioxide base material, the soft and flexible surface buffer layer to mitigate the difference in hardness between the bone and the base material, so that the soft surface further improves the bone adhesion characteristic. Therefore, the implant body receives an improved biocompatibility and a high bone attachment. In particular, a high bone attachment characteristic with respect to the alveolar bone is obtained by applying the implant body of the dental implant, which is inserted and fixes the implant body at the borehole in the alveolar bone.
    [19] Hereinafter follows a first embodiment of the implant body. the manufacturing method thereof and a dental implant according to the present invention to be described below with reference to Fig. 1 and Fig. 2.
    [20] The implant body 2 according to the present invention is an implant body fixed in contact configuration with the bone, as shown in Fig. 1, which is applied to an implant body for a dental implant 1 which is inserted and fixed in a borehole in the alveolar bone which functions as mentioned above. bone. The implant body 2 is formed substantially with a cylindrical shape with a tip which has a gradually decreasing outer diameter towards a lower part (distal end). The outer periphery of the implant body 2 forms a threaded trade 3. The threaded trade 3 is formed with a gradually varying shape with respect to the axial direction of the implant body 2.
    [21] A bracket (not shown) can be fixed with a connecting member, such as a thread structure, in an upper part of the implant body 2.
    [22] The implant body 2 shown in Fig. 2 is configured to form a base material 2a formed of zirconia and a surface layer 2b formed on the surface of the base material of zirconium hydroxide having a hardness lower than that of the base material 2a. A plurality of crack cavities W are formed in the surface layer 2b, and therefore further reduce the surface hardness.
    [23] Now, a manufacturing method for the implant body 2 of the dental implant will be described.
    [24] Then, a surface layer 2b of zirconium hydroxide is formed on the surface of the base material 2a by irradiating laser light into air containing moisture (in an atmosphere containing water vapor). The laser light used must be high energy laser light, and be, for example, laser light (with a fundamental wave) generated using a Nd: YAG laser or a YVO4 laser, which are semiconductor lasers.
    [25] During the irradiation with laser light, an adjustment is adjusted so that the hardness of the surface layer 2b becomes lower than or equal to the hardness of the alveolar bone. In other words, since the Vickers hardness of the alveolar bone is normally at the level of 500 Hv, the output or equivalent from the Nd: YAG laser or the YVO4 laser is set, according to the present embodiment, so that a surface layer is formed with a hardness of substantially 300 Hv. A blackened surface layer 2b is formed by the irradiation with laser light. '
    [26] When the implant body 2 and the dental implant 1 provided with the implant body 2 according to the present embodiment are provided with a base material 2a which is formed of zirconia and a surface layer 2b which has a lower hardness than the base material 2a and is formed on the surface of the base material 2a, in addition to having a mechanical strength superior to that of the zirconia base material 2a, the soft and flexible surface layer 2b acts as a buffer layer which mitigates the difference in hardness between the bone, such as the alveolar bone, and the base material 2a. In addition, the bone adhesion properties of the soft surface are improved.
    [27] In other words, an implant having a surface formed of a dense ceramic material [of high hardness in a conventional example has an upper limit on bone adhesion which is made possible by a simple roughening of the surface. In the implantation body 2 according to the present embodiment, however, the hardness of the surface layer 2b is reduced by said plurality of crack cavities W formed in the surface and bone cells can penetrate into an inner part through the crack cavities W. Thus, when bone cells penetrate, a high bone adhesion is possible and leg connection is made possible due to - the increase of the contact surface and the crosslinking effect.
    [28] When the hardness of the surface layer 2b is lower than or equal to the hardness of the bone, such as the alveolar bone, a hardness which is similar to the bone, such as the alveolar bone, or a surface which is softer and more flexible than bone, such as the alveolar bone, facilitates a tight adhesion of bone tissue. In addition, since the surface layer 2b is formed of zirconium hydroxide, a superior biocompatibility and high bone connection to bone tissue of the zirconium hydroxide of the surface layer 2b is enabled. In other words, the zirconium hydroxide of the surface layer 2b 'has an ion exchange effect which is believed to increase the number of' calcium ions and strengthen the growth of cells, as well as cause a significant improvement in bone adhesion.
    [29] Since the manufacturing method of the implant body 2 forms a surface layer 2b of zirconium hydroxide having a lower hardness than the base material Za on the surface of the zirconia base material 2a by laser irradiation of air containing moisture, the formation of a soft zirconium hydroxide surface layer 2 high adhesion property on the surface of the base material 2a is facilitated.
    [31] (Embodiment 1) In the following, the implant body, a manufacturing method of the implant body and one-tooth implants according to the present invention will be described in detail by means of working examples with reference to Fig. 3 to Fig. 12.
    [32] First, an unprocessed zirconia implant body without a hydroxide surface layer 2b processed using laser light as described above, and formed of an unmodified zirconia base material 2a for comparison purposes, and a zirconia implant body use of the laser light as described above as a working example. The irradiating laser light used a Nd: YAG laser as a ground wave. 'r
    [33] By applying infrared spectrophotometric analysis of the comparative example and the working example the results obtained are shown in Fig. 3. The curves showing the comparative example and the working example in the figure are shown with a vertical offset for simplified comparison.
    [34] Next, the results of a hardness measurement using a nano hardness tester (DLC film hardness measurement) are shown. A nano hardness tester is a measuring device that measures the load and hardness, and is set to an engraved depth of 1 μm. in
    [35] The results of two measurements of the Vickers hardness of the comparative example which is formed only by a zirconia base material 2a in 998 _Hv and 1129 Hv. In the working example, on the other hand, which forms a zirconium hydroxide surface layer 2b, the Vickers hardness was 336 Hv and 328 Hv. In other words, the hardness of the surface in the working example which forms a zirconium hydroxide surface layer 2b is clearly lower than the comparative example which is formed only by a zirconia base material 2a, and the surface is also soft in comparison with alveolar bones which normally have a hardness level of 500 Hv. The surface layer 2b of the implant body 2 of the working example is shown by SEM images captured using an electron microscope with different magnifications, as shown in Fig. 4 to Fig. 6. As shown in these SE1V1 images. a plurality of crack cavities W are generated in the surface layer 2b. i 10 15 20 25 '30 13
    [37] Then, in relation to the condition, four weeks after the implant body has actually been embedded in an experimental rat, the results can be observed in Fig. 7 to Fig. 12.
    [38] First, Fig. 7, Fig. 8 and Fig. 11 are enlarged photographic images of the main parts in cross section captured with an optical microscope as the comparative example used only includes the zirconia base material 2a. The solid black section of the enlarged photographic images represents the implant body, and the partially black piece on the periphery thereof is a bone component which has been stained with toluidine blue (the original photographic images are color images, and here the bone components are shown as blue). In contrast, Fig. 9, Fig. 10 and Fig. 12 are enlarged photographic images of the main parts in cross section captured with an optical microscope as the working example used forms a zirconium hydroxide surface layer 2b. The magnifications used in the pictures are as follows: Fig. 7 - 10 times, Fig. - 40 times, Fig. 9 - 10 times, Fig. 10 - 40 times, Fig. 11 - 150 times and Fig. 12 - 50 times - QBF- 'i'
    [39] In the comparative example and the working example, the results of the contact ratio between the surface 'of the implant body and the bone tissue of the comparative example are calculated to be 219%, as opposed to a contact ratio of the embodiment at 64.8%, which is consequently a significant improvement of the contact relationship. In this way, compared to using the implant body according to the comparative example, a large amount of newly formed bone tissue is observed in the periphery of the implant body when using the implant body according to the working example, and it turns out that a superior biocompatibility and a high leg connection are obtained. The regenerated bone in the periphery of the implantation body comes into direct contact with the implantation body and therefore causes so-called osseointegration.
    [40] The technical scope of the present invention is not limited by the above embodiments and various modifications may be added without departing from the spirit of the present invention.
    [41] For example, in the present embodiment, even if the laser irradiation was performed with laser light generated by a Nd: YAG laser or a YVO4-Easer, another type of laser may be used in that it is high energy laser light which allows the formation of a zirconium hydroxide surface layer. 2b of hydroxide formation on the surface of the zirconia base material 2a, for example laser light from another semiconductor laser or laser light from a harmonic wave.
    [42] In the present embodiment, the implanting body of the present invention is applied as an implanting body to a dental implant forming an artificial tooth root fixed by insertion into a borehole in the alveolar bone. however, the implant body can be applied as an implant body which is embedded or similarly inserted into bone in another region and fixed in a contact condition. For example, the implant body of the present invention can be applied as an artificial bone or bone filling material! in relation to an injury to the bone resulting from a fracture or removal of benign tumors, or to provide a cartilage supplement which has been removed due to lumbar spine surgery. In addition, the implant body of the present invention can be used in relation to a portion of an artificial joint, a bone connection material used to fix positions of a bone fracture or a spinal fixation apparatus. 15 (Description of the reference numbers) 1, 2 2a 2b Dental implants Implant body Base material Surface bearing Crack cavity
    权利要求:
    Claims (8)
    [1]
    An implant body fixed in a contact configuration with a bone, the implant body comprising: a base material formed of zirconia; a surface layer arranged on the surface of the base material and with a lower hardness than the base material.
    [2]
    The implant body according to claim 1, wherein a plurality of cracks are formed in the surface layer. “
    [3]
    The implant body of claim 1, wherein the hardness of the surface layer is less than or equal to the hardness of the bone.
    [4]
    The implant body of claim 1, wherein the surface layer is formed of zirconium hydroxide.
    [5]
    A dental implant body wherein the implant body of claim 1 is inserted into a borehole in the alveolar bone as an example of the bone. i '
    [6]
    A manufacturing method for an implant body which is fixed in a contact configuration with a bone, the method comprising the step of forming a zirconia hydroxide surface layer having a lower hardness than the base material on the surface of the zirconia base material by irradiation with laser light in air including moisture.
    [7]
    The manufacturing method of the implant body according to claim 6, wherein the laser light is laser light with a fundamental wave caused by a Nd: YAG laser or a YVO4 laser.
    [8]
    The manufacturing method of the implant body according to claim 6, wherein the hardness of the surface layer is lower than or equal to the hardness of the bone as a result of the irradiation with the laser light. '
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    法律状态:
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