201201870 六、發明說明： 【發明所屬之技術領域】 本發明係關於一種建構關於一生醫陶瓷骨骼支架(bio-ceramic bone scaffold) 之一立體模 型圖形 (three-dimensional mould graph)之建模方法(modeling method),以及根據該立體 模型圖形將該生醫陶竞骨路支架之成型方法（f〇rming method)。並且特別地，本發明係關於與真實的骨骼支架相同 具有内部多連通孔結構(inter-connective porous structure)之生 ^ 醫陶瓷骨骼支架其建模方法以及成型方法。 【先前技術】 快速原型(Rapid Prototyping, RP)成型技術使用堆疊加工 技術’能夠依照電腦辅助所建構的立體幾何圖形，自動製造 出二維實體物件的技術。快速原型成型技術可克服工具機加 工無法完成的幾何形狀死角，做到自動化實體自由形狀製造 (Solid Freeform Fabrication, SFF)，而且成型的原型沒有形狀 的限制。 鲁 快速原型成型設備所使用的成型工具分為兩大系統：雷 射系統以及喷嘴系統。一般利用喷嘴系統的快速原型成型設 備會有加工速度慢、材料容易阻塞，等缺點。舉例說明，屬 於噴嘴系統之炫解沉積法(Fusecj Deposition Modeling，FDM)裝 置能將，條狀的原料加熱成半熔化的狀態，再經由喷嘴擠出 材料堆疊成型，其製程所需的時間較長、效率差。同樣屬於 噴嘴系統之多喷嘴模型堆疊(Multi_Jet M〇dding，MJM)裝置利 用多喷嘴把黏結劑(binder)喷覆於粉末狀的材料上，黏結劑能 巧顆粒狀粉末餘起來，但是麟齡§阻塞。由於雷射 “月b里可凋整的範圍較大，一般而言，只要是粉末狀的原 3 201201870 料’快速原型成型設備都可以利用雷射光將其加以燒結或熔 結成型。 到目前為止，使用生醫材料與雷射光為加熱工具來製作 生醫組織工程支架的疊層加工技術可分為三大類：（1)立體微 影成像法(Stereolithography Apparatus, SLA):將生醫材料與紫 外光感光樹酯(UV resin)混合，經由紫外光雷射(uv Laser)掃 描固化後成型，（2)選擇性雷射燒結(seiective Laser Sintering， S^S):使用雷射光為熱源對粉末狀態的生醫材料進行選擇性 掃描，讓粉末顆粒之間產生燒結作用成型；以及(3)融熔沉積 製造(Fused Deposition Molding，FDM):利用嘖喈扣；^ 罂好μ 擠出依照歡路徑堆疊，可以製作出具有孔隙的1構/材料 在上述技術中，SLA採用紫外光感光樹酯做為黏結劑， 在做燒結後處理去除感光樹酯時會產生有害人體的氣體。 SLS使用雷射絲生醫材料進行燒結或直接麟形成工 件’因此’獅所受的雷射能量密雜大，容易 形。FDM雜能夠製作出交錯型式的網狀結構，= 狀的組織結構其上下層之間的接觸面積很小，強 内部===大織， 路支架之崎多賴聽_立雜_1=何建構關於骨 【發明内容】 陶:二體= 201201870 在於提供—種根據該立體模型 圖形將該生醫陶究骨路支架之成型方法 ^ 往快速成齡觀上關題。 避免上逑以 根據本發明之-較佳具體實施例的建模方法， =係用以建構關於-生醫較骨路支架之—立體模 ^ 特別地’與真實的錄支架相同，該生 ^ 首先係輸入 域尺寸。接者，該建财法餘據該生 該立體尺寸，建構一线。接著，該賴方法= 具有内部連通孔結構的立體模型單位元素圖形。接 耆I該建模方法係於該空間内，複製該至少—立體模型 】素，形’並鏈結該等且相鄰的立體模型單位元素圖形。最 =该建模方法係重複複製該立體模型單位元素圖形並鍵社 f等且相鄰的立體模型單位元素圖形之步驟，直至該等複^ 2體模型單位元素_填滿該空間。填滿該㈣之該等複 立體模型單位元素_即構成關於 之該立體模細形。 骑又永201201870 VI. Description of the Invention: [Technical Field of the Invention] The present invention relates to a modeling method for constructing a three-dimensional mould graph of a bio-ceramic bone scaffold (modeling) Method), and a method for forming the biomedical Taojing bone support according to the three-dimensional model graphic. And in particular, the present invention relates to a method and a molding method for a medical ceramic skeleton stent having an internal inter-connective porous structure, which is the same as a real bone skeleton. [Prior Art] Rapid Prototyping (RP) molding technology uses a stacking process technology to automatically create a two-dimensional physical object in accordance with computer-assisted solid geometry. Rapid prototyping technology overcomes the geometric dead angles that cannot be achieved with machine tool machining, and enables Solid Freeform Fabrication (SFF), and molded prototypes have no shape limitations. The forming tools used in the rapid prototyping equipment are divided into two major systems: the laser system and the nozzle system. Rapid prototyping equipment that typically utilizes a nozzle system has disadvantages such as slow processing speeds and easy material blockage. For example, the Fusecj Deposition Modeling (FDM) device belonging to the nozzle system can heat the strip material into a semi-melted state, and then extrude the material through the nozzle to form a stack, and the process takes a long time. Inefficient. The Multi_Jet M〇dding (MJM) device, which is also a nozzle system, uses a multi-nozzle to spray a binder onto a powdery material. The binder can be used as a granular powder. Blocked. Due to the large range of lasers that can be withered in the month b, in general, as long as the powder is the original 3 201201870 material, the rapid prototyping equipment can be sintered or sintered by laser light. The use of biomedical materials and laser light as heating tools to produce biomedical tissue engineering scaffolds can be divided into three categories: (1) Stereolithography Apparatus (SLA): Biomedical materials and UV Photosensitive resin (UV resin) mixed, cured by UV laser scanning, (2) seiective laser Sintering (S^S): using laser light as heat source to powder state The biomedical materials are selectively scanned to create a sintering effect between the powder particles; and (3) Fused Deposition Molding (FDM): using a buckle; ^Popular μ μ extrusion is stacked according to the Huan path It is possible to produce a structure/material with pores. In the above technique, SLA uses ultraviolet light-sensitive resin as a binder, which may cause harmful gas when processed to remove photosensitive resin. SLS uses laser biomedical materials for sintering or direct lining to form workpieces. Therefore, the laser energy of lions is dense and easy to shape. FDM hybrids can produce a staggered network structure, = tissue structure The contact area between the upper and lower layers is very small, strong internal === large weaving, the road bracket is more than the singular _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ _ According to the three-dimensional model figure, the method for forming the biomedical bone scaffold is fast-aged. The model is avoided according to the preferred embodiment of the present invention. Constructing the ---------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------------- Next, the Lai method = a solid model unit element graph with an internal connected pore structure. The modeling method is in the space, and the at least one-dimensional model is copied, and the shape is linked and the phase is Adjacent stereo model unit element The most = the modeling method is a step of repeatedly copying the solid model unit element graphic and the adjacent three-dimensional model unit element graphic until the complex model unit element_fills the space. Filling the (4) of the complex three-dimensional model unit elements _ constitutes the three-dimensional die shape.
N 據本發明之—較佳具體實施例的成型方法，該成型方 據該立體模型圖形將該生醫陶兗骨絡支架成型-二、康鋒认究骨路支？之一陶竟生^(eeramic green body)係由iN 二々的陶瓷固態薄層(⑽mic solid film)所構成，其中n為 立。该成型方法首先係輸人該立體模型圖形，並將言亥 柰&圖形剖切成Ν層二維戴面圖案，該Ν層二維截面圖 :二〇·應該N層陶細態薄層中之一層喊固態薄層。接 μ成型方法係將一生物相容陶瓷粉末(bi〇_c〇mpa仙^ B ：l^C/_^Γ)與一陶究溶膠(Ceramic so1)依一比例均勻混合 料於_!成一ί料(SlUri7。接著，該成型方法係塗佈第一層漿 、工作台上。接著，該成型方法係根據對應該第一層陶 201201870 ίί從m f層漿料於第_漿料上，/係 應該第，層陶紙態薄型方f係根據對 庫了 熱使該陶:光溶膠產生該化學凝膠反 成該第，層陶兗固態薄層。接著，該成;;法J f複塗佈第Z層漿料之步驟以及以該雷射 艰、 驟’直至完成該N層陶組態薄層為止。，ii 得附ΐΤ N層陶究固態薄層之前漿料，以ί 。最後’該成型方法係烘乾該陶竞生述，並對 進仃該陶瓷生坯燒結即完成該生醫陶瓷骨骼支架。 0巧ΐ前技術相較，根據本發明之建模方法可以自動、有 構關於生醫喊骨路支架之立體模型圖形，並且^ 才^、有不同的支架結構、孔洞形狀、尺寸大小、密度與孔隙 t立，模麵形，以觀真實的㈣支架結構，以利細胞 =耆、成長。根據本發明之成型方法利於均勻鋪設出厚度較 溥的漿料層，並且可避免於後續清洗過程中產生有宝物質且 ，用較小能量即能引發的化學凝膠反應，減少對材^的熱衝 擊。根據本發明之成型方法所製作的生醫陶瓷骨骼 且 足夠的機械強度β 、 關於本發明之優點與精神可以藉由以下的發明 附圖式得到進一步的瞭解。 【實施方式】 201201870 請參閱圖一’圖一係繪示根據本發明之一佳具體實施 之建模方法1的流程圖。根據本發明之建模方法丨係用以 構關於-生醫陶究骨路支架之—立體模型圖形。特別地，斑 真實的骨路支架相同’該生醫喊修支架具有内部多連^ 孔結構。 如圖一所示，根據本發明之建模方法丨首先係執 S10，輸入該生醫陶瓷骨骼支架之一立體尺寸。 乂鄉 同樣示於圖…接著’根據本發明之建模方法i係 步驟S12 ’根據該生醫陶究骨路支架之該立體尺寸，一 空間。 舟 同樣示於圖-’接著’根據本發明之建模方法丨係 步驟S14，設計至少-具有内部連通孔結構的立體^ 元素圖形。 早位 請參閱圖二A，具有内部連通孔結構的立體 素圖形的範例如圖二A中標示2Ga〜2Qi之圖形。早位几 同樣示關…接著，根據本發明 步驟S16，於該空間内’複製該至少一立體模型單位 形，並賴鱗且鱗社_辟位元疋素圖 同樣示於圖- ’接著，根據本發 步驟S18，判斷鱗複製的立體模 素執行 建模方法1係重複執行步驟S16， 月之 方 若步驟S18的判斷結果為奴者，根據本發明之建模 7 201201870 ^ 1係執行步驟S19，結束複製該立體模型單位元素圖形。 藉此，填滿該空間之該等複製的立體模型單位元素圖形即構 成關於該生醫陶瓷骨骼支架之該立體模型圖形。 ,明參閱圖二B，關於該生醫陶瓷骨路支架之立體模型圖 形之局部圖形的範例如圖二B中標示2a〜2g之圖形。特別 地，圖二B中之關於該生醫陶瓷骨骼支架之該立體模型圖形 局部圖形(2a〜2g)皆具有内部連通孔結構。 請參閱圖三以及圖四A至四C ’圖三係繪示根據本發明 之一較佳具體實施例之成型方法3的流程圖。根據本發明之 成型方法3用以根據本發明之建模方法所建構之立體模型圖 形將該生醫陶瓷骨骼支架成型。特別地，該生醫陶瓷骨骼支 架之一陶瓷生坯係由N層連續的陶瓷固態薄層所構成，其中 N為一自然數。圖四A至四C係繪示運用可實施本發明之成 型設備4來成型該生醫陶瓷骨骼支架之陶瓷生坯的成型示意 圖。According to the molding method of the preferred embodiment of the present invention, the molding method forms the biomedical ceramic skeleton and the bone scaffold according to the three-dimensional model figure-two, Kang Feng recognizes the bone branch? One of the eeramic green bodies is composed of a ceramic solid layer of (i) bismuth, where n is erect. The forming method firstly inputs the three-dimensional model figure, and cuts the 柰 柰 amp & graphics into a Ν layer two-dimensional wearing pattern, the 二维 layer two-dimensional sectional view: two 〇 · should N layer ceramic thin layer One of the layers shouted a solid thin layer. The μ molding method is to uniformly mix a biocompatible ceramic powder (bi〇_c〇mpaxian^B: l^C/_^Γ) with a ceramic so1 (Ceramic so1) in a ratio of _! Lai material (SlUri7. Next, the molding method is applied to the first layer of slurry, on the workbench. Then, the molding method is based on the first layer of pottery 201201870 ίί from the mf layer slurry on the first slurry, / The system should be in the first layer, the ceramic layer of the thin layer f is based on the heat of the library, the ceramic: the photo-sol is generated by the photo-sol, and the layer is a solid layer of the ceramic layer. Then, the method; The step of coating the Z-thick slurry and the laser is difficult until the completion of the N-layer ceramic configuration thin layer. ii has the N-layer ceramic solid layer before the slurry, to ί. Finally 'The molding method is to dry the Tao Jingsheng, and to complete the sintering of the ceramic green body to complete the biomedical ceramic skeleton support. Compared with the prior art, the modeling method according to the present invention can be automatically and structurally related. The doctors call the three-dimensional model figure of the bone road bracket, and ^ ^ ^, have different bracket structure, hole shape, size, density With the pores t-shaped, the die-face shape, to observe the real (four) scaffold structure, in order to facilitate cell = 耆, growth. The molding method according to the present invention facilitates uniform laying of a thicker slurry layer and can avoid subsequent cleaning processes A chemical gel reaction which is generated by a small amount of energy and which reduces the thermal shock of the material. The biomedical ceramic skeleton produced by the molding method of the present invention has sufficient mechanical strength β, about the present The advantages and spirit of the invention can be further understood by the following description of the invention. [Embodiment] 201201870 Please refer to FIG. 1A. FIG. 1 is a flow chart showing a modeling method 1 according to a preferred embodiment of the present invention. The modeling method according to the present invention is used to construct a three-dimensional model figure of the biomedical bone support. In particular, the real bone support of the spot is the same. Hole structure. As shown in Fig. 1, according to the modeling method of the present invention, firstly, S10 is executed, and one of the three-dimensional dimensions of the biomedical ceramic skeleton support is input. The township is also shown in the figure... According to the modeling method i of the present invention, the step S12' is based on the stereoscopic dimension of the biomedical bone support, a space. The boat is also shown in the figure - 'Next', according to the modeling method of the present invention, step S14, Design at least a three-dimensional ^ element pattern with an internal communication hole structure. Refer to Figure 2A for an early position. An example of a three-dimensional pattern with an internal communication hole structure is shown in Figure 2A. Figure 2A shows the pattern of 2Ga~2Qi. And then, according to the step S16 of the present invention, the at least one stereo model unit form is copied in the space, and the scale and the scale element are also shown in the figure - 'Next, according to the step S18 of the present invention The scalar mode execution modeling method for judging the scale copy 1 is repeatedly performed in step S16, and if the result of the step S18 is a slave, the model 7 201201870 ^ 1 according to the present invention performs step S19 to end the copy. Stereo model unit element graphic. Thereby, the replicated solid model unit element graphic filling the space constitutes the three-dimensional model graphic of the biomedical ceramic skeleton scaffold. Referring to Figure 2B, an example of a partial pattern of the three-dimensional model of the biomedical ceramic bone support is shown in Fig. 2B as a pattern of 2a to 2g. In particular, the three-dimensional model graphic partial patterns (2a to 2g) of the biomedical ceramic skeleton support in Fig. 2B have an internal communication hole structure. Referring to Figure 3 and Figures 4A through 4C', Figure 3 is a flow chart showing a molding method 3 in accordance with a preferred embodiment of the present invention. The molding method 3 according to the present invention is used to mold the biomedical ceramic skeleton scaffold according to the three-dimensional model pattern constructed by the modeling method of the present invention. In particular, the ceramic green body of one of the biomedical ceramic skeleton supports is composed of a continuous ceramic solid layer of N layers, wherein N is a natural number. 4A to 4C are schematic views showing the molding of a ceramic green body in which the biomedical ceramic skeleton support is formed by using the molding apparatus 4 which can implement the present invention.
如圖三所示，根據本發明之成型方法3首先係執行步驟 S30，輸入該立體模型圖形，並將該立體模型圖形剖切成N 層二維截面圖案’其中該N層二維截面圖案依序對應該n層 陶瓷固態薄層中之一層陶瓷固態薄層。 曰 同樣示於圖三’接著，根據本發明之成型方法1係執行 步驟S31，製備一生物相容陶瓷粉末以及一陶瓷溶膠。 於一具體實施例中，該生物相容陶瓷粉末可以是氳氧基 磷灰石(Hydroxyapatite，HA)、三鈣磷酸鹽、氫氧基磷灰石二 甲殼素、鱗灰石(Apatite)、金雲母(Fluoro-Phlogopite)、石夕灰石 (Wollastonite)、氧化i呂、Κ20、Na20、CaO、P205、Si〇2、As shown in FIG. 3, the molding method 3 according to the present invention first performs step S30, inputs the three-dimensional model graphic, and cuts the three-dimensional model graphic into an N-layer two-dimensional sectional pattern, wherein the N-layer two-dimensional sectional pattern is The order corresponds to one layer of ceramic solid layer in the n-layer ceramic solid layer.曰 Also shown in Fig. 3' Next, the molding method 1 according to the present invention performs step S31 to prepare a biocompatible ceramic powder and a ceramic sol. In a specific embodiment, the biocompatible ceramic powder may be Hydroxyapatite (HA), tricalcium phosphate, hydroxyapatite, tartar (Apatite), gold. Mm. (Fluoro-Phlogopite), Wollastonite, Oxidation, Lu 20, Na20, CaO, P205, Si〇2
MgO，等粉末’或上述材料的混合組合之粉末。生物相容陶 201201870 瓷粉末的粒徑可視成型工件的尺寸而定，例如至 45μπι ° 於一具體實施例中，該陶瓷溶膠可以是氧化矽溶膠、氧 化鈦溶膠、氧化紹溶膠、氧化結溶膠，等陶究溶膠，或上 陶瓷溶膠的混合組合。 接著，根據本發明之成型方法3係執行步驟S32，將該 生物相容陶瓷粉末與該陶瓷溶膠依一比例均勻混合，且 成一漿料。 免干A powder of MgO, a powder of the same or a combination of the above materials. The particle size of the biocompatible pottery 201201870 porcelain powder may depend on the size of the shaped workpiece, for example to 45 μm. In one embodiment, the ceramic sol may be a cerium oxide sol, a titanium oxide sol, a oxidized sol, an oxidized sol, Such as ceramic sol, or a combination of ceramic sol. Next, according to the molding method 3 of the present invention, the step S32 is carried out, and the biocompatible ceramic powder and the ceramic sol are uniformly mixed in a ratio to form a slurry. Free of dry
θ於一具體實施例中，生物相容陶瓷粉末與該陶瓷溶膠之 重量百分比為 60wt%:40wt% 〜30\^%:7〇^%。 於-具體實施射，該祕之祕為3G〜5_%生物相容 陶究粉末、10〜15wt〇/〇溶劑、35〜55wt%陶究溶膠以及2〜5wt% 懸洋劑。該溶劑為水，懸浮劑為六偏雜鈉[啊灿]、 j鱗酸邮a她G)或微粒雲母。料料的 1200 cp 至 3000 cP。 在抽接如圖二及圖四A所示’根據本發明之成型方法3 ，執仃步驟S34 ’以-塗層裝置42塗佈第一層襞料於一 :41^°^工胃作台44具有—平面，且被致動沿垂直該平面 軸之，做升降。根據本發明， 裝漿料sl的漏斗422以及可使漿 44上的顺424_城滾筒) 該漏斗422擠送適當的漿料SL，至該工作纟44上。） =將之漿料SL，塗佈成均勻的薄層漿料sl，。每:層5 ^涂=可控制在約G.lmm。但本發明不以此為限，所需 亦即塗層厚度係可變者。例如，“大 201201870 時，塗層厚度則變小 裝料為限。 。並且本發明亦不以水平或等厚度塗佈 接著，如圖三及圖四B所示，根據本發明之成型方法3 係執行步驟S36，根據對應該第一層陶瓷固態薄層SL"之第一 層二維截面圖案，以一固態薄膜形成裝置46所發射之一雷射 光束照射該第-層聚料SL，之部分紐SL，，其中該第一層毁 =SL·被該雷射光束照射之部分漿料SL，被加熱使該陶瓷 產•生一化學凝膠反應，進而形成該第一層陶瓷固態薄層 SL’’(圖四B中深色部分）。也就是說，随轉脫水而形成i J分子結#(例如：Si_asi、AK)_A1)，再進—步發展為網狀 =子結構，當其成長觸及生物相容陶瓷粉末時，即將生物相 谷陶瓷粕末緊祗包覆並黏結在一起。而相鄰層間亦以該陶究 :谷膠產生化學凝膠反應而黏結在一起。於化學凝膠反應完成 後，即形成立體的陶瓷生坯。由於未使用有機黏結劑，因此 在去除餘料和後續的燒結製程中不會產生有害氣體。由於使 該，f* ^膠產生化學凝膠反應所需能量遠小於燒結陶瓷粉末 所需能量，因此可大幅降低陶瓷工件收縮及變形的影響。 如圖四B所示，該固態薄膜形成裝置46包含一雷射光 ，產生裝置462、一導光機構464以及一聚焦鏡460。該雷射 光束產生裝置462用以產生一雷射光束，例如，c〇2雷射、 Nd:YAG雷射、He-Cd雷射、Ar雷射或UV雷射。於一具體 實施例中，該雷射光束產生裝置462可以加裝溫度感測器， 當溫度感測器偵測到用來冷卻該雷射光束產生裝置462之冷 卻水溫度超過25。(：時，該雷射光束產生裝置462即停止雷射 光的激發。 與先前技術利用振鏡式掃描讓雷射光束聚焦在每一層漿 料SL'方法不同’該導光機構464與該聚焦鏡466根據對應每 201201870 -層陶細_層SL”之截_案被致動平行如圖四 之X-Y平面移動。該導光機構464帛以導 ^ 聚焦鏡466。該聚焦鏡466用以聚焦該雷射光 『sy 具體實施例中，雷射光束的掃描速“ 85mm/s、掃描間距為〇.lmm，雷射功率為1〇w。於一且ς 施例中，於該聚焦鏡466處可以加裝一噴氣管。喷^ ^ 導入低壓空氣並經由其喷嘴快速喷出， 漿料濺散附著於聚焦鏡片上，影響雷 同樣示於圖四Β，根據本發明之導光機構464包含多個 固疋的反射鏡以及能被致動平行如圖四Β所示之χ_γ =反射鏡。例如’圖四Β中標示464a及_標號代表固 疋的反射鏡’標示464e標號代表能被致動沿平 ， ί 1 轴反射鏡，標示_號代=跟隨^ _能沿平拥四B _之Y軸之-軸移動的 射鏡。邊聚焦鏡466則伴隨該反射鏡464d 一起移動。 装實施例中，根據本發明之固態薄膜形成裝置46 ί ^η掃描的工作範圍為麵Χ 250 _，最高速度 ，3000 mm/min以上’且其χ-γ軸重複精度設計為± 002 地，與糊振鏡式掃鄕11縣錢賴先前技術 .本發明之固態薄膜形成裝置46，其設計即可改ϋ先 則技術其工作範圍小與雷射光絲錢衫足的缺點。° 孫抽，ί ’ *圖二及圖四C所^ ’根據本發明之成型方法3 ^執行步驟S38，致動該工作台44沿平行圖四c中ζ轴之一 距離(一個薄層的厚度），使得在後續塗佈完新的一 j ’不必重行調整該111態賊形成裝置46的聚焦基 。v驟S38中，並且執行戶(/+1)的運算。此外需強調的 201201870 是，於實際應用中，每一層陶瓷固態薄層不以相同厚度為必 要。 接著，如圖三所示，根據本發明之成型方法3係執行步 驟S40，以該塗層裝置42塗佈第/層漿料於第(w)層漿料 上，/係範圍從2至N中之一整數指標。隨後，根據本發明 之成型方法3係執行步驟S42，根據對應該第層陶究固態薄 層SL之第/層二維截面圖案，以該固態薄膜形成裝置所 發射之雷射光束照射該第/層漿料SL’之部分漿料SL，。同樣 地，該第/·層祕SL，觀雷射絲照射之部分祕SL，被加 熱使該，究溶膠產生該化學凝膠反應，進而形成該第層陶 1 :實務上’經由。雇技術，可將電腦與將該 線，依據料二賴面®案控繼_薄膜形 造。、 對母一層聚料SL’加熱，並進-步達成自動化製 掃 === ==係 —距離(一個_厚度)，接續執行步驟ί。及以S42 了降 法的觸結果騎定者，根據本發明之成型方 係執仃步驟S46 ,以一.峪 B及圖四C中)去除附菩於兮M、^置(未、，、曰不於圖四A、圖四 料SL，，以獲N層陶兗固態薄層SL”之殘留聚 之局例二之=所製造的陶細 201201870 於實際應用中，因為使用喊漿料本身做 躲贼具有_連通 根據本發明之成型方法3係執行步驟撕，洪乾 u瓷生坯，並對進行該陶瓷生坯燒結，即完成該生醫陶瓷 lii架:根據本發明之生醫陶堯骨骼支架為具有内 其可以依照不同的3D模型圖，製作出具有特定孔 尺寸大小的骨路支架。—般適合細胞附著、成長之 士4組織的孔隙尺寸為60〇iUm〜1(%m之間。實務上，根據 發明之成型方法所製造的多孔性生醫陶瓷骨骼支架可以製 #出具有孔隙度範圍$ 200〜800//m的孔隙，以利細胞附 者、成長。 於一具體實施例中，該生物相容陶瓷粉末係三鈣磷酸鹽 (列如’磷酸詞)或！>2〇5 ’於燒結製程中，該陶瓷生坯可以被 =熱至1200。(：以上，利用熔滲方式進行燒結。藉此，可以提 =該生醫陶瓷骨骼支架的機械性質，其抗彎強度可由3MPa 升至16MPa以上’同時增加生物活性(bi〇activ^y)。 λ綜上所述，本發明所建構關於生醫陶瓷骨骼支架之立體 模型圖形，具有不同的支架結構、孔洞形狀、尺寸大小、密 ^與孔隙度’以模擬真實的骨骼支架結構，以利細胞附著、 長。本發明採用的材料狀態為漿料狀態，具有一定的流動 ’兼具固態材料和液態材料的優點，可均勻混合陶瓷溶膠 …生物相容陶瓷粉末’並利於均勻鋪設出厚度較薄的漿料 13 201201870 ，描方式可改善先前技術其“ 述本藉發 施例來對本發明之$l加嫌制。相反地，其目的是 涵蓋^種改變及具相等性的安排於本發明所欲申請之專利^ 圍的範疇内。因此，本發明所申請之專利範圍的範疇應診= 據上述的說明作最寬廣的解釋，以致使其涵蓋所有可^ 變以及具相等性的安排。 、文 201201870 【圖式簡單說明】 程圖圖—錄據本發明之—較佳具體實施例之建模方法的流 圖形結獅域翻單位元素θ In one embodiment, the weight percentage of the biocompatible ceramic powder to the ceramic sol is 60% by weight: 40% by weight to 30% by weight: 7% by weight. In the specific implementation, the secret of the secret is 3G~5_% biocompatible ceramic powder, 10~15wt〇/〇 solvent, 35~55wt% ceramic sol and 2~5wt% suspension agent. The solvent is water, and the suspending agent is hexamethylene sodium [ahcan], j squamous acid a her G) or particulate mica. The material is from 1200 cp to 3000 cP. In the drawing, as shown in FIG. 2 and FIG. 4A, the molding method 3 according to the present invention, the step S34 is performed, and the first layer of the coating material is applied by the coating device 42 to: 41^°^ 44 has a plane and is actuated along the axis perpendicular to the plane for lifting. In accordance with the present invention, the funnel 422 of the slurry sl and the funnel 422 of the slurry 44 can be squeezed onto the appropriate slurry SL onto the working crucible 44. ) = Coating the slurry SL into a uniform thin layer slurry sl. Each layer: 5 ^ coating = can be controlled at about G.lmm. However, the invention is not limited thereto, and it is required that the coating thickness be variable. For example, "in the case of 201201870, the thickness of the coating becomes smaller and the charging is limited. And the present invention is not coated with a horizontal or equal thickness, as shown in Fig. 3 and Fig. 4B, the molding method 3 according to the present invention. Step S36 is performed to irradiate the first layer of the polymer SL with a laser beam emitted by a solid film forming device 46 according to the first two-dimensional cross-sectional pattern corresponding to the first layer of the ceramic solid layer SL" a portion of the New SL, wherein the first layer is destroyed = SL. a portion of the slurry SL irradiated by the laser beam is heated to cause the ceramic to react with a chemical gel to form the first layer of the ceramic solid layer SL'' (dark part in Figure 4B). That is to say, i J molecular knot # (for example: Si_asi, AK)_A1) is formed by dehydration, and then further developed into a network = substructure, when When the growth touches the biocompatible ceramic powder, the bio-phase ceramics are coated and bonded together, and the adjacent layers are also bonded together by the chemical reaction of the gluten. After the gel reaction is completed, a three-dimensional ceramic green body is formed. The organic binder is used, so no harmful gas is generated during the removal of the residual material and the subsequent sintering process. Since this, the energy required for the chemical gel reaction of the f*^ gum is much smaller than that required for the sintered ceramic powder, so The effect of shrinking and deforming the ceramic workpiece is reduced. As shown in Fig. 4B, the solid film forming device 46 includes a laser beam, a generating device 462, a light guiding mechanism 464, and a focusing mirror 460. The laser beam generating device 462 is used. To generate a laser beam, such as a c〇2 laser, a Nd:YAG laser, a He-Cd laser, an Ar laser or a UV laser. In one embodiment, the laser beam generating device 462 can A temperature sensor is installed, and when the temperature sensor detects that the temperature of the cooling water for cooling the laser beam generating device 462 exceeds 25 (::, the laser beam generating device 462 stops the excitation of the laser light. Compared with the prior art, the galvanometer scanning is used to focus the laser beam on each layer of the slurry SL'. The light guiding mechanism 464 and the focusing mirror 466 are according to the corresponding per-201201870 - layer ceramic layer _ layer SL. Actuation parallel as shown in Figure 4. The XY plane moves. The light guiding mechanism 464 is used to guide the focusing mirror 466. The focusing mirror 466 is used to focus the laser light "sy. In the specific embodiment, the scanning speed of the laser beam is "85 mm/s, and the scanning pitch is 〇. Lmm, the laser power is 1〇w. In the case of the embodiment, a jet tube can be installed at the focusing mirror 466. The nozzle is introduced into the low-pressure air and quickly ejected through the nozzle, and the slurry is splashed and attached. On the focusing lens, the influence lightning is also shown in Fig. 4. The light guiding mechanism 464 according to the present invention comprises a plurality of solid mirrors and can be actuated in parallel as shown in Fig. 4 χ γ = mirror. For example Figure Β 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 464 The axis-axis movement of the mirror. The side focusing mirror 466 moves with the mirror 464d. In the embodiment, the solid-state film forming apparatus according to the present invention scans the working range of the surface Χ 250 _, the highest speed, 3000 mm/min or more and the χ-γ axis repeatability is designed to be ± 002 ground. With the paste mirror broom 11 county Qian Lai prior art. The solid film forming device 46 of the present invention can be designed to improve the shortcomings of the prior art and the shortcomings of the laser light. ° Sun pumping, ί ' * Figure 2 and Figure 4 C ^ 'Molding method 3 according to the invention ^ Step S38 is performed to actuate the table 44 along a distance parallel to the axis of Figure 4 c (a thin layer The thickness is such that it is not necessary to re-adjust the focus base of the 111-state thief-forming device 46 after the subsequent coating of a new one. v in step S38, and the operation of the household (/+1) is performed. In addition, 201201870 is emphasized. In practical applications, each layer of ceramic solid layer is not necessary to have the same thickness. Next, as shown in FIG. 3, the molding method 3 according to the present invention performs step S40, and applies the first layer slurry to the (w) layer slurry by the coating device 42, and the range is from 2 to N. One of the integer indicators. Subsequently, according to the molding method 3 of the present invention, the step S42 is performed, and the laser beam emitted by the solid-state film forming device is irradiated to the / according to the first/layer two-dimensional cross-sectional pattern corresponding to the first layer of the solid-state thin layer SL. Part of the slurry SL of the layer slurry SL'. Similarly, the first layer SL, the part of the secret SL irradiated by the laser, is heated to cause the sol to generate the chemical gel reaction, thereby forming the first layer of ceramics 1 : practically. Hiring technology, the computer and the line can be controlled according to the material. , heating the parent layer SL', and further automating the sweep === == system - distance (one thickness), and then proceeding to step ί. And the result of the S42 drop method of the rider, according to the molding method of the present invention, the step S46 is performed, and the sputum is removed from the 兮M, ^, (,,,,曰 曰 图 A A A A 图 图 图 图 图 图 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 2012 Doing the thief has _ connected according to the molding method of the present invention 3 is to perform the steps of tearing, squeezing the porcelain green body, and sintering the ceramic green body, that is, completing the biomedical ceramic lii frame: according to the invention The skeletal scaffold has a bone scaffold with a specific pore size according to different 3D model maps. The pore size of the tissue suitable for cell attachment and growth is 60〇iUm~1 (%m In practice, the porous biomedical ceramic skeleton scaffold manufactured according to the molding method of the invention can produce pores having a porosity ranging from $200 to 800/m, in order to facilitate cell attachment and growth. In an embodiment, the biocompatible ceramic powder is a tricalcium phosphate (such as 'phosphorus Word) or !>2〇5 'In the sintering process, the ceramic green body can be heated to 1200. (: Above, sintering is performed by infiltration method. Thereby, the biomedical ceramic skeleton scaffold can be Mechanical properties, the flexural strength can be increased from 3 MPa to more than 16 MPa' while increasing the biological activity (bi〇activ^y). λ In summary, the three-dimensional model figures of the biomedical ceramic skeleton support constructed by the present invention have different Scaffold structure, pore shape, size, density and porosity 'to simulate the real bone scaffold structure to facilitate cell attachment and length. The material state used in the present invention is a slurry state with a certain flow 'both solid materials And the advantages of the liquid material, can uniformly mix the ceramic sol ... biocompatible ceramic powder 'and facilitate the uniform laying of the thin thickness of the slurry 13 201201870, the method can improve the prior art, "the present borrowing example to the present invention </ RTI> <RTIgt; </ RTI> <RTIgt; </ RTI> <RTIgt; </ RTI> <RTIgt; </ RTI> <RTIgt; </ RTI> <RTIgt; </ RTI> <RTIgt; Scope of scope consultation = The broadest explanation based on the above description, so that it covers all the arrangements that can be changed and equal., 201201870 [Simple diagram of the diagram] The diagram of the diagram - the recording of the present invention - The flow pattern of the modeling method of the preferred embodiment is a lion domain unit element
之^職型圖形 程圄圖二係根據本發明之—較佳具體實施例之成型方法的流 在塗之趟賴來姻喊生链其 生本發明之成型方法所製造的喊生述之局部 【主要元件符號說明】 1 .建模枝 S1G〜S19 :方法步驟 2a〜2g .立體模型圖形之局部圖形 〇a 20i ·立體模型單位元素圖形 15 201201870 3:成型方法 S30〜S48 :方法步驟 4:成型設備 42 :塗層裝置 422 :漏斗 424 :刮板 44 :工作台 46 :固化薄層形成裝置 462 :雷射光束產生裝置 464 :導光機構 464a、464b、464c、464d :反射鏡 466 :聚焦鏡 5a〜5f:陶瓷生坯之局部生坯 SL :漿料 SL” ：陶瓷固態薄層 SL’ ：漿料層Figure 2 is a partial representation of a molding method according to the present invention - a preferred embodiment of the molding method in the coating method of the coating method of the present invention. Description of component symbols] 1. Modeling branches S1G to S19: Method steps 2a to 2g. Partial graphics of stereo model graphics 〇a 20i · Stereo model unit element graphics 15 201201870 3: Molding method S30 to S48: Method step 4: Molding equipment 42: Coating device 422: Funnel 424: Scraper 44: Table 46: Curing thin layer forming device 462: Laser beam generating device 464: Light guiding mechanism 464a, 464b, 464c, 464d: Mirror 466: Focusing mirror 5a ~5f: Partial green body SL of ceramic green body: Slurry SL": Ceramic solid thin layer SL': slurry layer