JPS61226053A - Production of living body material - Google Patents

Abstract

(57) [Summary] This bulletin contains application data before electronic filing, so abstract data is not recorded.

Description

DETAILED DESCRIPTION OF THE INVENTION The present invention "G" relates to a method for producing biomaterials, particularly biomaterials used as artificial bones, artificial tooth crowns, artificial tooth roots, etc.

Conventionally, materials for artificial bone and dental implants include metal materials such as silver and tantalum, alloy materials such as cobalt chlorine alloy, titanium alloy, and stainless steel, and polymer materials such as polymethyl methacrylate and high-strength polyethylene. has been used. However, although metals and alloy materials have excellent strength,
It has poor affinity with living tissues, and if used in the human body for a long period of time, metal ions will be dissolved and may harm living tissues.
In addition, although the polymer 4111'l is stable in vivo, it has low strength and does not chemically bond with bones, so it can only be used in very limited areas, and it also contains residual unreacted particles during manufacturing.
There was a risk that it would elute and damage living tissue. On the other hand,
Ceramic materials such as alumina ceramics have excellent strength and biocompatibility, and there is little risk that the components eluted from them will have a negative effect on the human body, so they are used as artificial bones and dental materials R1. 1] It has become like 2. However, since alumina ceramic does not form a chemical bond with bone, if the shape of the heptadramic hole that allows new bone to enter is not properly shaped, l'ij may occur in the bone or in a part of the ceramic.
``There was a risk that the concentration of force would cause the bone to be absorbed or the ceramic to be destroyed.Therefore, as a ceramic material that creates a chemical bond with the bone, Na, 07 CaO-
8]○! I couldn't think of 17+Os crystallized glass or apatite sintered K, but these have low mechanical strength or
It has the disadvantage that it is not easy to manufacture.

The present invention has been made in order to improve the drawbacks listed in item L, and aims to provide a method for manufacturing a biomaterial that has high mechanical strength, is compatible with living tissue, and firmly adheres to bone. The target is

The bio-friendly manufacturing method of the present invention involves coating the outer surface of a zirconia ceramic sintered body or a preformed body of zirconia ceramic powder with PtO*-Oa, Q thread glass powder, and then heating it at 1000 to 1700°C. It is characterized by being made by firing.

PtO5 used in the biomaterial manufacturing method of the present invention
-C! a, o The preferred composition of the thread glass powder is % by weight
and at least P+0g 1-30%, Oa, 020
~53%, Sj, 0t20~56%, 111g01~
20%, and 50.0 to 20%. This glass powder crystallizes during firing and becomes crystallized glass in which apatite, wollastonite, and diopside crystal phases are precipitated.

1°105. The reason for limiting the preferred composition range of CaO-based glass as described above is as follows.

'P, if it is less than 1%, the precipitation of apatite, which is a potassium ricinate crystal, will be small (and the biocompatibility will be low), and if it is more than 30%, it will be devitrified. Becomes stronger and puts out Wolastonite at 17 years old 4: "Yes.

C a. When Q is less than 20% (1), the crystallinity (fil) decreases, and fewer apatite and sub-wall crystals (only 1) are precipitated, while when it is more than 53%, the crystallinity decreases. If the permeability is high, vitrification becomes difficult.

Sj. When 0□ is less than 20% (J1 devitrification becomes high, making it difficult to melt and mold the glass, and when it is more than A lastite, the viscosity of the glass becomes high and it becomes difficult to melt.) In both cases, the amount of apatite crystal precipitation decreases.

When MgO is less than 1%, the 6:J devitrification becomes high, making vitrification difficult and the amount of di-subite crystals precipitated is small, and when it is more than 20%, the crystallization rate is slow. This results in lower crystallinity and mechanical strength.

B203 has the effect of promoting the fluidity of glass, and has the effect of softening and fluidizing during the firing process to wet the outer surface of the zirconia ceramic powder that becomes the core material and the zirconia ceramic fin body and form a strong bond. However, if it exceeds 20%, the devitrification becomes strong and a homogeneous glass cannot be obtained.

This glass powder is produced by melting raw material powders mixed to a predetermined composition in an electric furnace for 1450 4 hrs.
It is obtained by making a ribbon glass using a water-cooled roller and pulverizing it into 280 meshes using an alumina ball mill.

This PtO5-OaO glass powder is coated on the outer surface of a zirconia ceramic fired body or a zirconia ceramic preform, and is then crystallized by heat treatment to form a large number of apatite, wollastonite, and diopside microcrystals in the glass. The result is a structure in which is precipitated. The apatite crystals in this crystallized glass create a chemical bond with bone and improve biocompatibility, and the lastnitite crystals have the effect of increasing the mechanical strength of the crystallized glass.

In the present invention, zirconia ceramic is selected and used among various ceramics because it has high strength and excellent adhesion to the Psis-OaO glass coated on the surface of the base. This zirconia ceramic contains Zr0 65 to 9 in weight%.
3%, Y. 032 to 15%, with a small amount of Alvoa, 0130.

It is preferable to contain. In the production method of the present invention, the raw material powder having the above composition is 1450-16'OO''
A zirconia ceramic sintered body that has already been heated at C or a preformed body whose raw material powder has not yet been fired are used.

The method for producing a biomaterial of the present invention includes adding PtO,=CaoCaO glass powder to a zirconia ceramic sintered body or a zirconia ceramic powder preform, and then
1] is fired at 1000 to 1700'C.

When using a zirconia ceramic sintered body, the firing temperature is 1000 to 200°C, the temperature at which the glass powder softens and flows, adheres to the ceramic sintered body, and crystallizes. On the other hand, when a preformed body of unfired zirconia ceramic powder is used, the firing temperature is a relatively high temperature of 1200 to 1700°C at which the zirconia ceramic powder sufficiently becomes a fired body. In the latter case, the zirconia ceramic powder and the glass powder are fired at the same time, and after this firing, the desired crystalline phase is sufficiently precipitated to transform the glass powder into crystallized glass with high mechanical strength. 1000～
A glass crystallization heat treatment step is carried out in which the glass is maintained at a temperature of 1200° C. for a predetermined period of time.

The present invention will be explained in detail below.

Example 1 In weight%, Zr0180%, 0eO115%, y, o,
After thoroughly mixing the ceramic powder consisting of 5%,
This is hydrostatically pressed into a cylindrical shape with a diameter of 5 mm and a length of 10 mm to form a preform. This preformed body has a diameter of 7
P, 0510%, Ca, 030% in a mold tank that was placed in a round container with a diameter of 2 mm and granulated to about 50% in a gap of 2 mm.
, 5iO14・5%, l11g010%, ■3□035
%, filled with 280% glass powder and pressed. The glass powder was taken out of the container and further hydrostatically pressed to bond the glass powder to the surface of the core to a thickness of about 1000/1.
When 111 is sintered, the inside becomes a zirconia ceramic sintered body, and the glass powder on the surface softens and flows to become glass that is strongly fixed to the internal zirconia ceramic sintered body. Furthermore, by firing at 100° C. for 2 hours, the surface glass layer becomes an apatite and wollastonite crystallized glass layer.

Example 2 ZrO□, C84 Y2O mixed in the same proportion as Example
8 powder was hydrostatically pressed into a cylindrical shape and fired at 1500°C for 3 hours. The obtained zirconia ceramic sintered body was processed into a cylinder with a diameter of 5 m + n and a length of 10 mm, and then
Place it in the center of a cylindrical container with an empty capacity of 1 tlft 1 mm.
The glass powder granulated in the same manner as in Example 1 is filled into the glass powder and pressed. When this is removed from the container and further subjected to isostatic pressing, the glass powder is pressed onto the zirconia ceramic sintered body that is the core material. This material coated with glass powder]
] When fired at 00° C. for 2 hours, the glass powder softens and flows, becomes fixed to the surface of the zirconia ceramic resintered body, and forms a crystallized glass layer in which apatite and wollastonite crystals are precipitated.

The biomaterials obtained in Examples 1 and 2 showed a high bending strength of 5,000 to 7,000 kg/(7), and even after 8 weeks had elapsed after inserting this material into a bone defect. No harm was shown and adhesion to natural bone was good.

Claims (2)

[Claims] (1) P_2O_5- on the outer surface of the zirconia ceramic sintered body or the zirconia ceramic powder preform
1000-1700 after coating with CaO-based glass powder
A method for producing biomaterials by firing at °C. (2) P_2O_5-CaO glass powder has at least P_2O_51-30% and CaO20-53% by weight.
%, SiO_220-56%, MgO1-20%, B_
2. The method for producing a biomaterial according to claim 1, characterized in that the biomaterial contains 30 to 20% of 2O_30.