CN115671384A - 一种骨修复支架及其制备方法和应用 - Google Patents
一种骨修复支架及其制备方法和应用 Download PDFInfo
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- CN115671384A CN115671384A CN202110841435.9A CN202110841435A CN115671384A CN 115671384 A CN115671384 A CN 115671384A CN 202110841435 A CN202110841435 A CN 202110841435A CN 115671384 A CN115671384 A CN 115671384A
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- Prior art keywords
- bone repair
- scaffold
- manganese
- repair scaffold
- dimensional porous
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Abstract
本发明公开了一种骨修复支架及其制备方法和应用,所述骨修复支架为三维多孔支架,所述骨修复支架的材料包括以下质量百分比的组分:80%~95%的可生物降解聚合物和5%~20%的可生物降解纳米颗粒,所述可生物降解纳米颗粒为锰的化合物纳米颗粒。所述骨修复支架的制备方法包括:按照所述质量百分比配制包含可生物降解聚合物和可生物降解纳米颗粒的均相溶液;将所述均相溶液通过固化成型工艺制备获得成型的三维多孔支架;将所述成型的三维多孔支架冷冻干燥,获得所述骨修复支架。本发明提供的骨修复支架能够更好地促进骨损伤愈合,并且具有优异的力学性能和良好地医学影像成像效果。
Description
技术领域
本发明涉及生物医学工程技术领域,具体涉及一种骨修复支架及其制备方法和应用。
背景技术
随着骨科治疗技术的发展,临床骨科疾病的治愈率及疗效不断提高,但仍有一些骨缺损由于多种原因不能按时愈合。此外,严重骨折伴随的骨缺损、肿瘤术后骨缺损,以及脊柱融合等的治疗均离不开骨修复和再生过程。传统的自体骨移植可基本满足以上要求,临床疗效可靠,长期以来是治疗骨折不愈合和骨缺损的金标准。但自体骨移植存在供区并发症、来源有限等问题,因此人们不断探索和尝试各种替代方法以促进骨修复和骨再生。利用可生物降解聚合物通过打印制备获得兼具生物相容性、可降解性、力学性能良好的骨修复支架是目前组织工程支架的研究热点。
左旋聚乳酸(PLLA)作为一种典型的生物可降解高分子材料,具有来源广泛,降解产物无毒以及良好的生物相容性等优点。然而,采用PLLA制备获得的骨修复支架力学强度相对不足、植入缺损部位后医学成像质量低等特点限制了其在骨修复领域中的应用。
发明内容
有鉴于此,本发明提供了一种骨修复支架及其制备方法和应用,以解决现有的骨修复支架力学强度相对不足、植入缺损部位后医学成像质量低的问题。
为了实现上述目的,本发明采用了如下的技术方案:
一种骨修复支架,所述骨修复支架为三维多孔支架,所述骨修复支架的材料包括以下质量百分比的组分:80%~95%的可生物降解聚合物和5%~20%的可生物降解纳米颗粒,所述可生物降解纳米颗粒为锰的化合物纳米颗粒。
优选地,所述锰的化合物选自选自二氧化锰、四氧化三锰、葡萄糖酸锰、氯化锰、乙酸锰、磷酸二氢锰、碳酸锰、硫酸锰和羰基锰中的一种或两种以上。
优选地,所述锰的化合物纳米颗粒的粒径为1nm~1000nm。
优选地,所述可生物降解聚合物选自聚乳酸-羟基乙酸共聚物、聚乳酸、聚乳酸-乙醇酸和聚己内酯中的一种或两种以上。
优选地,所述三维多孔支架中的微孔的孔径为300μm~500μm,所述三维多孔支架的孔隙率为60%~80%。
优选地,所述微孔至少贯通所述三维多孔支架的两个相对的表面。
本发明的另一方面是提供一种如上所述的骨修复支架的制备方法,其包括:
按照所述质量百分比配制包含所述可生物降解聚合物和所述可生物降解纳米颗粒的均相溶液;
将所述均相溶液通过固化成型工艺制备获得成型的三维多孔支架;
将所述成型的三维多孔支架冷冻干燥,获得所述骨修复支架。
优选地,所述配制包含所述可生物降解聚合物和所述可生物降解纳米颗粒的均相溶液的步骤中,所述可生物降解聚合物和所述可生物降解纳米颗粒的结合方式为搅拌混合或化学反应的方式;所述固化成型工艺为3D打印成型工艺、熔融沉积成型工艺、模板成型工艺或添加制孔剂成型工艺。
优选地,所述固化成型工艺为3D打印成型工艺,所述将所述均相溶液通过固化成型工艺制备获得成型的三维多孔支架包括:
利用设计软件创建模型并获取相应的打印参数;
将所述均相溶液加入至3D打印设备中,按照所述打印参数打印成型,得到成型的三维多孔支架;
其中,所述打印参数包括:喷丝间距为0.4mm~2mm,打印层高为0.08mm~0.16mm,喷头移动速度为1mm/s~20mm/s,喷头出料速度为0.1mm3/s~1mm3/s,打印温度为-40℃~-20℃;所述冷冻干燥的温度为-40℃~-100℃,时间为24h~72h。
本发明还提供了一种如上所述的骨修复支架在成骨和医学成像中的应用。
本发明实施例中提供的骨修复支架及其制备方法,具有如下的有益效果:
(1)、骨修复支架的材料为添加了锰的化合物纳米颗粒的可生物降解聚合物,锰的化合物可以消耗微环境中过量的过氧化氢,生成对修复有益的氧气及锰离子,将其应用于骨损伤治疗中,不仅可以消耗损伤部位的过氧化氢抑止炎症反应发生,同时也能提高损伤部位的氧含量,提高成骨细胞的活性,促进骨损伤愈合,并且锰离子的促成骨作用可以进一步加快骨损伤愈合过程。
(2)、通过添加锰的化合物纳米颗粒,制备获得的骨修复支架具有更高的压缩强度和压缩模量,具有优异的力学性能。进一步地,添加的锰的化合物具有优异的CT成像功能,有效地提高了骨修复支架的医学影像成像效果。
(3)、所述骨修复支架为三维多孔支架结构,具有很高孔隙率,使得其有利于成骨细胞生长,附着,增殖等,同时支架的多孔结构可诱导骨长入。因此其作为引导骨再生的骨修复支架,在骨缺损治疗领域具备很大的应用价值。
附图说明
图1是本发明实施例1制备获得的骨修复支架的结构示意图;
图2是本发明实施例1制备获得的骨修复支架的横截面示意图;
图3是本发明对比例制备获得的骨修复支架的结构示意图;
图4是本发明测试例中对测试样品A进行CT成像的影像图示;
图5是本发明测试例中对测试样品B进行CT成像的影像图示。
具体实施方式
为使本发明的目的、技术方案和优点更加清楚,下面结合附图对本发明的具体实施方式进行详细说明。这些优选实施方式的示例在附图中进行了例示。附图中所示和根据附图描述的本发明的实施方式仅仅是示例性的,并且本发明并不限于这些实施方式。
在此,还需要说明的是,为了避免因不必要的细节而模糊了本发明,在附图中仅仅示出了与根据本发明的方案密切相关的结构和/或处理步骤,而省略了与本发明关系不大的其他细节。
如前文所述,针对现有的采用可生物降解聚合物(例如PLLA)制备获得的骨修复支架力学强度相对不足、植入缺损部位后医学成像质量低的问题,本发明实施例提出了一种骨修复支架及其制备方法,通过在可生物降解聚合物中添加锰的化合物纳米颗粒,使得骨修复支架能够更好地促进骨损伤愈合,并且具有优异的力学性能和良好地医学影像成像效果。
本发明实施例首先提供了一种骨修复支架,所述骨修复支架是通过打印成型的三维多孔支架,所述骨修复支架的材料包括以下质量百分比的组分:
80%~95%的可生物降解聚合物,例如可以选择为80%、82%、85%、88%、90%、93%或95%的可生物降解聚合物;
5%~20%的可生物降解纳米颗粒,例如是5%、7%、10%、12%、15%、18%或20%的可生物降解纳米颗粒。其中,所述可生物降解纳米颗粒为锰的化合物纳米颗粒。
骨修复支架的材料为添加了锰的化合物纳米颗粒的可生物降解聚合物,锰的化合物纳米颗粒可以消耗微环境中过量的过氧化氢,生成对修复有益的氧气及锰离子,将其应用于骨损伤治疗中,不仅可以消耗损伤部位的过氧化氢抑止炎症反应发生,同时也能提高损伤部位的氧含量,提高成骨细胞的活性,促进骨损伤愈合,并且锰离子的促成骨作用可以进一步加快骨损伤愈合过程。
进一步地,通过添加锰的化合物纳米颗粒,制备获得的骨修复支架具有更高的压缩强度和压缩模量,具有优异的力学性能。并且,添加的锰的氧化物纳米颗粒具有优异的CT成像功能,有效地提高了骨修复支架的医学影像成像效果。
在具体的方案中,所述锰的化合物选自选自二氧化锰、四氧化三锰、葡萄糖酸锰、氯化锰、乙酸锰、磷酸二氢锰、碳酸锰、硫酸锰和羰基锰中的一种或两种以上,优选为锰的氧化物纳米颗粒,例如是二氧化锰颗粒或四氧化三锰颗粒。优选地,所述锰的化合物纳米颗粒的粒径为1nm~1000nm,例如是1nm、5nm、10nm、50nm、100nm、200nm、300nm、500nm、800nm或1000nm,更为优选的是所述锰的化合物纳米颗粒的粒径为100nm~300nm。
在具体的方案中,所述可生物降解聚合物选自聚乳酸-羟基乙酸共聚物(PLGA)、聚乳酸(PLA)、聚乳酸-乙醇酸(PLGA)和聚己内酯(PCL)中的一种或两种以上。
在一个优选的方案中,所述可生物降解聚合物选择为左旋聚乳酸(PLLA),所述可生物降解纳米颗粒为二氧化锰颗粒。进一步优选的,所述骨修复支架的材料包括以下质量百分比的组分:95%的左旋聚乳酸和5%的二氧化锰颗粒。
在具体的方案中,所述三维多孔支架中的微孔的孔径为300μm~500μm,所述三维多孔支架的孔隙率为60%~80%。该结构的骨修复支架具有很高孔隙率,使得其有利于成骨细胞生长,附着,增殖等,同时骨修复支架的多孔结构可诱导骨长入。
优选的方案中,所述微孔至少贯通所述三维多孔支架的两个相对的表面。例如,所述微孔在所述三维多孔支架的高度方向上贯通上下两个表面。
本发明实施例提供了一种如上所述的骨修复支架的制备方法,所述制备方法包括以下步骤:
S10、按照如上文所述的质量百分比配制包含所述可生物降解聚合物和所述可生物降解纳米颗粒的均相溶液。
在具体地方案中,所述可生物降解聚合物和所述可生物降解纳米颗粒的结合方式为搅拌混合或化学反应的方式。
优选使用搅拌混合的方式,具体是:按照如上文所述的质量百分比称取可生物降解聚合物和可生物降解纳米颗粒溶解于有机溶剂中,搅拌混合获得均相溶液。
S20、将所述均相溶液通过固化成型工艺制备获得成型的三维多孔支架。
具体地,所述固化成型工艺可以选择为3D打印成型工艺、熔融沉积成型工艺、模板成型工艺或添加制孔剂成型工艺;优选使用3D打印工艺。
在优选的方案中,所述固化成型工艺为3D打印工艺。其中,步骤S10配制均相溶液的过程中,有机溶剂可选择为现有的任意一种有利于3D打印成型的有机溶剂,溶解的过程可在40℃~60℃的温度下进行,优选为55℃。
其中,采用3D打印工艺制备获得成型的三维多孔支架包括以下步骤:
S21、利用设计软件创建模型并获取相应的打印参数。
在一个具体的方案中,利用低温快速成型设备适配的BioMakerV2软件创建模型,得到三维立体结构模型;导出三维立体结构模型的数据,利用分层软件将所述数据进行分层处理以得到分层后的数据,根据分层后的数据设置相应的打印参数。
在一些优选的方案中,所述打印参数包括:喷丝间距为0.4mm~2mm,打印层高为0.08mm~0.16mm,喷头移动速度为1mm/s~20mm/s,喷头出料速度为0.1mm3/s~1mm3/s,打印温度为-40℃~-20℃。在一个具体的技术方案中,所述打印参数优选为:喷丝间距为1mm,打印层高为0.12mm,喷头移动速度为10mm/s,喷头出料速度为0.5mm3/s,打印温度为-30℃。
S22、将所述均相溶液加入至3D打印设备中,按照所述打印参数打印成型,得到成型的三维多孔支架。
通过打印成型的三维多孔支架,可以根据骨缺损形状设计不同结构的骨修复支架。其中,通过调整所述打印参数,可以使得所述三维多孔支架中的微孔的孔径为300μm~500μm,例如是300μm、350μm、400μm、450μm或500μm,所述三维多孔支架的孔隙率为60%~80%。
S30、将所述成型的三维多孔支架冷冻干燥,获得所述骨修复支架。
在一些优选的方案中,所述冷冻干燥的温度为-40℃~-100℃,时间为24h~72h。
鉴于本发明实施例提供的骨修复支架具有提高成骨细胞的活性而促进骨损伤愈合的性能以及良好的成像功能,本发明实施例还提供了如上所述的骨修复支架在成骨和医学成像(包括CT、MRI、PET等)中的应用。
实施例1
本实施例的骨修复支架的材料由如下质量百分比的组分组成:95%的PLLA和5%的二氧化锰纳米颗粒。
上述复合骨修复支架的制备方法,包括以下步骤:
(1)、按照质量百分比,称取95%的PLLA、5%的粒径为100nm的二氧化锰纳米颗粒置于烧杯之中,然后加入1,4-二氧六环,搅拌以形成均相溶液。其中PLLA在1,4-二氧六环中的浓度为0.125g/mL。
(2)、利用低温快速成型设备适配的BioMakerV2软件创建模型,创建例如2×2×2cm3的立方体结构模型;导出三维立体结构模型的数据,利用分层软件将所述数据进行分层处理以得到分层后的数据。
(3)、将步骤1得到的均相溶液加入至低温快速成型设备的物料罐中并装配好,根据步骤2的分层后的数据设置打印参数,其中喷丝间距为1mm,层高为0.12mm,喷头移动速度为10mm/s,喷头出料速度为0.5mm3/s,在-30℃下进行打印成型,得到2×2×2cm3的三维多孔支架;
(4)、将所述成型的三维多孔支架在冷冻干燥机中在-100℃的温度下冻干24h,得到骨修复支架。
图1是本实施例制备获得的骨修复支架的结构示意图,由于添加了质量百分比为5%二氧化锰纳米颗粒,制备获得的骨修复支架呈浅灰色,其孔隙、颜色均一。
图2是本实施例制备获得的骨修复支架的横截面示意图,通过显微镜对所述骨修复支架进行截面的微观形貌观察,该骨修复支架具有贯通上下表面的孔隙。
实施例2
本实施例的骨修复支架的材料由如下质量百分比的组分组成:80%的PLA和20%的二氧化锰纳米颗粒。
上述复合骨修复支架的制备方法,包括以下步骤:
(1)、按照质量百分比,称取80%的PLA、20%的粒径为200nm的二氧化锰纳米颗粒置于烧杯之中,然后加入二甲基亚砜(DMSO),搅拌以形成均相溶液。其中PLA在DMSO中的浓度为0.1g/mL。
(2)、利用Solidworks软件创建模型,创建例如3×3×3cm3的立方体结构模型;导出三维立体结构模型的数据,利用分层软件将所述数据进行分层处理以得到分层后的数据。
(3)、将步骤1得到的均相溶液加入至低温快速成型设备的物料罐中并装配好,根据步骤2的分层后的数据设置打印参数,其中喷丝间距为1.1mm,层高为0.1mm,喷头移动速度为20mm/s,喷头出料速度为0.3mm3/s,在-25℃下进行打印成型,得到3×3×3cm3的三维多孔支架;
(4)、将所述成型的三维多孔支架在冷冻干燥机中在-85℃的温度下冻干48h,得到骨修复支架。
实施例3
本实施例的骨修复支架的材料由如下质量百分比的组分组成:90%的PLGA和10%的二氧化锰纳米颗粒。
上述复合骨修复支架的制备方法,包括以下步骤:
(1)、按照质量百分比,称取90%的PLGA、10%的粒径为150nm的二氧化锰纳米颗粒置于烧杯之中,然后加入1,4-二氧六环,搅拌以形成均相溶液。其中PLGA在1,4-二氧六环中的浓度为0.15g/mL。
(2)、利用Solidworks软件创建模型,创建例如2.5×2.5×2.5cm3的立方体结构模型;导出三维立体结构模型的数据,利用分层软件将所述数据进行分层处理以得到分层后的数据。
(3)、将步骤1得到的均相溶液加入至低温快速成型设备的物料罐中并装配好,根据步骤2的分层后的数据设置打印参数,其中喷丝间距为1.2mm,层高为0.15mm,喷头移动速度为15mm/s,喷头出料速度为0.35mm3/s,在-28℃下进行打印成型,得到2.5×2.5×2.5cm3的三维多孔支架;
(4)、将所述成型的三维多孔支架在冷冻干燥机中在-80℃的温度下冻干48h,得到骨修复支架。
实施例4
本实施例的骨修复支架的材料由如下质量百分比的组分组成:95%的PLLA和5%的葡萄糖酸锰纳米颗粒。
上述复合骨修复支架的制备方法,包括以下步骤:
(1)、按照质量百分比,称取95%的PLLA、5%的粒径为100nm的葡萄糖酸锰纳米颗粒置于烧杯之中,然后加入1,4-二氧六环,搅拌以形成均相溶液。其中PLLA在1,4-二氧六环中的浓度为0.125g/mL。
(2)、利用低温快速成型设备适配的BioMakerV2软件创建模型,创建例如2×2×2cm3的立方体结构模型;导出三维立体结构模型的数据,利用分层软件将所述数据进行分层处理以得到分层后的数据。
(3)、将步骤1得到的均相溶液加入至低温快速成型设备的物料罐中并装配好,根据步骤2的分层后的数据设置打印参数,其中喷丝间距为1mm,层高为0.12mm,喷头移动速度为10mm/s,喷头出料速度为0.5mm3/s,在-30℃下进行打印成型,得到2×2×2cm3的三维多孔支架;
(4)、将所述成型的三维多孔支架在冷冻干燥机中在-80℃的温度下冻干24h,得到骨修复支架。
实施例5
本实施例的骨修复支架的材料由如下质量百分比的组分组成:95%的PLLA和5%的氯化锰纳米颗粒。
上述复合骨修复支架的制备方法,包括以下步骤:
(1)、按照质量百分比,称取95%的PLLA、5%的粒径为100nm的氯化锰纳米颗粒置于烧杯之中,然后加入1,4-二氧六环,搅拌以形成均相溶液。其中PLLA在1,4-二氧六环中的浓度为0.125g/mL。
(2)、利用低温快速成型设备适配的BioMakerV2软件创建模型,创建例如2×2×2cm3的立方体结构模型;导出三维立体结构模型的数据,利用分层软件将所述数据进行分层处理以得到分层后的数据。
(3)、将步骤1得到的均相溶液加入至低温快速成型设备的物料罐中并装配好,根据步骤2的分层后的数据设置打印参数,其中喷丝间距为1mm,层高为0.12mm,喷头移动速度为10mm/s,喷头出料速度为0.5mm3/s,在-30℃下进行打印成型,得到2×2×2cm3的三维多孔支架;
(4)、将所述成型的三维多孔支架在冷冻干燥机中在-80℃的温度下冻干24h,得到骨修复支架。
对比例
对比例与实施例1的区别在于:骨修复支架的材料仅包含有PLLA,不添加二氧化锰纳米颗粒。其余材料及工艺过程参照实施例1进行,制备获得对比例骨修复支架样品。
图3是对比例制备获得的骨修复支架的结构示意图,由于没有添加锰的氧化物纳米颗粒,制备获得的骨修复支架呈PLLA的原色(白色),其孔隙均一。
测试例
参照实施例1-5和对比例1分别制备获得测试样品A1-A5和测试样品B。
其中,测试样品A1与实施例1的骨修复支架样品的区别为样品尺寸增大为10×10×10cm3;测试样品A2与实施例2的骨修复支架样品的区别为样品尺寸增大为10×10×10cm3;测试样品A3与实施例3的骨修复支架样品的区别为样品尺寸增大为10×10×10cm3;测试样品A4与实施例4的骨修复支架样品的区别为样品尺寸增大为10×10×10cm3;测试样品A5与实施例5的骨修复支架样品的区别为样品尺寸增大为10×10×10cm3;测试样品B与对比例的骨修复支架样品的区别为样品尺寸增大为10×10×10cm3。
针对测试样品进行如下的测试:
(1)、压缩强度和压缩模量的测试
使用万能力学试验机进行测试,加压速度为1mm/min。测试样品A1-A5和测试样品B分别选取4个样品,测试结果取平均值。具体测试结果如表1所示。
表1
由表1的数据可以看出:在没有加入锰的化合物纳米颗粒之前,骨修复支架的压缩强度在1.7MPa左右,压缩模量在30MPa左右;在添加了锰的化合物纳米颗粒之后,骨修复支架的压缩强度和压缩模量都有较大的提升。由此可见,添加了锰的化合物纳米颗粒能够明显地提高骨修复支架的压缩强度和压缩模量。因此本发明实施例所提供的骨修复支架具有更好的力学性能,能够在骨填充中起到更好的支撑作用。
(2)、医学成像效果测试
采用micro-CT分别扫描了测试样品A1和测试样品B,利用系统内置软件CT-Analyser重建并分析。图4为测试样品A1的CT成像的示例性图示,图5为测试样品B的CT成像的示例性图示。对比图4和图5可以看出,在同样的扫描以及重建参数下,测试样品A1相比于测试样品B具有更清晰的成像效果。因此本发明实施例所提供的骨修复支架具有更好的医学成像效果,在CT下成像更清晰。
综上所述,本发明实施例中提供的骨修复支架及其制备方法,通过在可生物降解聚合物中添加锰的化合物纳米颗粒,使得骨修复支架能够更好地促进骨损伤愈合,并且具有优异的力学性能和良好地医学影像成像效果。
以上所述仅是本申请的具体实施方式,应当指出,对于本技术领域的普通技术人员来说,在不脱离本申请原理的前提下,还可以做出若干改进和润饰,这些改进和润饰也应视为本申请的保护范围。
Claims (10)
1.一种骨修复支架,其特征在于,所述骨修复支架为三维多孔支架,所述骨修复支架的材料包括以下质量百分比的组分:80%~95%的可生物降解聚合物和5%~20%的可生物降解纳米颗粒,所述可生物降解纳米颗粒为锰的化合物纳米颗粒。
2.根据权利要求1所述的骨修复支架,其特征在于,所述锰的化合物选自选自二氧化锰、四氧化三锰、葡萄糖酸锰、氯化锰、乙酸锰、磷酸二氢锰、碳酸锰、硫酸锰和羰基锰中的一种或两种以上。
3.根据权利要求1所述的骨修复支架,其特征在于,所述锰的化合物纳米颗粒的粒径为1nm~1000nm。
4.根据权利要求1所述的骨修复支架,其特征在于,所述可生物降解聚合物选自聚乳酸-羟基乙酸共聚物、聚乳酸、聚乳酸-乙醇酸和聚己内酯中的一种或两种以上。
5.根据权利要求1-4任一所述的骨修复支架,其特征在于,所述三维多孔支架中的微孔的孔径为300μm~500μm,所述三维多孔支架的孔隙率为60%~80%。
6.根据权利要求5所述的骨修复支架,其特征在于,所述微孔至少贯通所述三维多孔支架的两个相对的表面。
7.一种如权利要求1-6任一所述的骨修复支架的制备方法,其特征在于,包括:
按照所述质量百分比配制包含所述可生物降解聚合物和所述可生物降解纳米颗粒的均相溶液;
将所述均相溶液通过固化成型工艺制备获得成型的三维多孔支架;
将所述成型的三维多孔支架冷冻干燥,获得所述骨修复支架。
8.根据权利要求7所述的骨修复支架的制备方法,其特征在于,所述配制包含所述可生物降解聚合物和所述可生物降解纳米颗粒的均相溶液的步骤中,所述可生物降解聚合物和所述可生物降解纳米颗粒的结合方式为搅拌混合或化学反应的方式;所述固化成型工艺为3D打印成型工艺、熔融沉积成型工艺、模板成型工艺或添加制孔剂成型工艺。
9.根据权利要求8所述的骨修复支架的制备方法,其特征在于,所述固化成型工艺为3D打印成型工艺,所述将所述均相溶液通过固化成型工艺制备获得成型的三维多孔支架包括:
利用设计软件创建模型并获取相应的打印参数;
将所述均相溶液加入至3D打印设备中,按照所述打印参数打印成型,得到成型的三维多孔支架;
其中,所述打印参数包括:喷丝间距为0.4mm~2mm,打印层高为0.08mm~0.16mm,喷头移动速度为1mm/s~20mm/s,喷头出料速度为0.1mm3/s~1mm3/s,打印温度为-40℃~-20℃;所述冷冻干燥的温度为-40℃~-100℃,时间为24h~72h。
10.权利要求1-6任一所述的骨修复支架在成骨和医学成像中的应用。
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