CN1418974A - Method for synthesizing NiTi shape memory alloy porous material - Google Patents
Method for synthesizing NiTi shape memory alloy porous material Download PDFInfo
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- 229910001000 nickel titanium Inorganic materials 0.000 title claims abstract description 35
- 238000000034 method Methods 0.000 title claims abstract description 15
- 239000011148 porous material Substances 0.000 title description 9
- 229910001285 shape-memory alloy Inorganic materials 0.000 title description 9
- 230000002194 synthesizing effect Effects 0.000 title 1
- 239000000956 alloy Substances 0.000 claims abstract description 26
- 229910045601 alloy Inorganic materials 0.000 claims abstract description 25
- 239000000843 powder Substances 0.000 claims abstract description 22
- 238000003786 synthesis reaction Methods 0.000 claims abstract description 20
- 238000002347 injection Methods 0.000 claims abstract description 18
- 239000007924 injection Substances 0.000 claims abstract description 18
- 239000000463 material Substances 0.000 claims abstract description 16
- 238000005238 degreasing Methods 0.000 claims abstract description 14
- 230000015572 biosynthetic process Effects 0.000 claims abstract description 12
- 239000011230 binding agent Substances 0.000 claims abstract description 10
- 238000006243 chemical reaction Methods 0.000 claims abstract description 9
- 239000002994 raw material Substances 0.000 claims abstract description 7
- 239000002904 solvent Substances 0.000 claims abstract description 7
- 238000002156 mixing Methods 0.000 claims abstract description 6
- 229910052751 metal Inorganic materials 0.000 claims description 15
- 239000002184 metal Substances 0.000 claims description 14
- 238000001746 injection moulding Methods 0.000 claims description 11
- 239000000203 mixture Substances 0.000 claims description 5
- 239000012188 paraffin wax Substances 0.000 claims description 3
- 238000000498 ball milling Methods 0.000 claims description 2
- 238000001035 drying Methods 0.000 abstract 1
- 238000004898 kneading Methods 0.000 abstract 1
- 238000005516 engineering process Methods 0.000 description 10
- PXHVJJICTQNCMI-UHFFFAOYSA-N nickel Substances [Ni] PXHVJJICTQNCMI-UHFFFAOYSA-N 0.000 description 10
- 239000010936 titanium Substances 0.000 description 9
- KHYBPSFKEHXSLX-UHFFFAOYSA-N iminotitanium Chemical compound [Ti]=N KHYBPSFKEHXSLX-UHFFFAOYSA-N 0.000 description 7
- 210000000988 bone and bone Anatomy 0.000 description 6
- 229910052759 nickel Inorganic materials 0.000 description 5
- 229910052719 titanium Inorganic materials 0.000 description 5
- 239000000047 product Substances 0.000 description 4
- XKRFYHLGVUSROY-UHFFFAOYSA-N Argon Chemical compound [Ar] XKRFYHLGVUSROY-UHFFFAOYSA-N 0.000 description 2
- MCMNRKCIXSYSNV-UHFFFAOYSA-N Zirconium dioxide Chemical compound O=[Zr]=O MCMNRKCIXSYSNV-UHFFFAOYSA-N 0.000 description 2
- 239000000919 ceramic Substances 0.000 description 2
- 230000006835 compression Effects 0.000 description 2
- 238000007906 compression Methods 0.000 description 2
- 239000012467 final product Substances 0.000 description 2
- 230000005484 gravity Effects 0.000 description 2
- 239000007943 implant Substances 0.000 description 2
- 229910000765 intermetallic Inorganic materials 0.000 description 2
- 238000004519 manufacturing process Methods 0.000 description 2
- 238000004663 powder metallurgy Methods 0.000 description 2
- 238000002360 preparation method Methods 0.000 description 2
- 239000010935 stainless steel Substances 0.000 description 2
- 229910001220 stainless steel Inorganic materials 0.000 description 2
- 238000001308 synthesis method Methods 0.000 description 2
- 229910001030 Iron–nickel alloy Inorganic materials 0.000 description 1
- 229910001069 Ti alloy Inorganic materials 0.000 description 1
- 229910001315 Tool steel Inorganic materials 0.000 description 1
- PNEYBMLMFCGWSK-UHFFFAOYSA-N aluminium oxide Inorganic materials [O-2].[O-2].[O-2].[Al+3].[Al+3] PNEYBMLMFCGWSK-UHFFFAOYSA-N 0.000 description 1
- 229910052786 argon Inorganic materials 0.000 description 1
- 238000002485 combustion reaction Methods 0.000 description 1
- 150000001875 compounds Chemical class 0.000 description 1
- 238000001816 cooling Methods 0.000 description 1
- 230000007797 corrosion Effects 0.000 description 1
- 238000005260 corrosion Methods 0.000 description 1
- 238000009826 distribution Methods 0.000 description 1
- 238000010438 heat treatment Methods 0.000 description 1
- 230000010354 integration Effects 0.000 description 1
- 230000005389 magnetism Effects 0.000 description 1
- 239000011812 mixed powder Substances 0.000 description 1
- 231100000956 nontoxicity Toxicity 0.000 description 1
- 239000003960 organic solvent Substances 0.000 description 1
- 230000001681 protective effect Effects 0.000 description 1
- 238000005245 sintering Methods 0.000 description 1
- 229910000601 superalloy Inorganic materials 0.000 description 1
- 210000001519 tissue Anatomy 0.000 description 1
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Abstract
本发明提供了一种注射成形—自蔓延高温合成NiTi合金多孔体材料的方法，特征在于：以Ti粉和Ni粉为原料，混合均匀后与粘结剂(30～50％Vol)在混炼机上混炼，然后制粒成喂料，注射成坯件，再将其浸入汽油中溶剂脱脂，烘干后放入真空炉热脱脂，最后将坯件一端与点火装置的W丝相连接，放入真空反应合成器中，真空度高于1×10－2Pa时开始升温，达到设定温度后启动点火装置，即发生自蔓延高温合成反应，得到产品。优点在于：所制备的NiTi合金孔隙度为40～60％，开孔率85％以上，抗压强度为85.5～321.0Mpa，可压缩应变量为1.7～3.6％，抗拉强度为21.3～78.5MPa，延伸率为3.0～6.7％。
The invention provides a method for injection molding-self-propagating high-temperature synthesis of NiTi alloy porous body material, which is characterized in that: Ti powder and Ni powder are used as raw materials, mixed evenly with binder (30-50% Vol) in kneading Mixing on the machine, then granulating into feed, injecting into a blank, then immersing it in gasoline for solvent degreasing, drying, putting it into a vacuum furnace for thermal degreasing, and finally connecting one end of the blank to the W wire of the ignition device, and putting Into the vacuum reaction synthesizer, when the vacuum degree is higher than 1× 10-2 Pa, the temperature starts to rise, and when the set temperature is reached, the ignition device is started, that is, a self-propagating high-temperature synthesis reaction occurs, and the product is obtained. The advantages are: the porosity of the prepared NiTi alloy is 40-60%, the opening ratio is more than 85%, the compressive strength is 85.5-321.0Mpa, the compressible strain is 1.7-3.6%, and the tensile strength is 21.3-78.5MPa , The elongation rate is 3.0-6.7%.
Description
技术领域technical field
本发明属于注射成形—自蔓延高温合成(Self-propagating High-temperatureSynthesis，缩写SHS)NiTi合金技术领域，特别是提供了一种注射成形—自蔓延高温合成NiTi合金多孔体材料的方法。The invention belongs to the field of injection molding-self-propagating high-temperature synthesis (Self-propagating High-temperature Synthesis, abbreviated as SHS) NiTi alloy technology, and in particular provides a method for injection molding-self-propagating high-temperature synthesis of NiTi alloy porous body materials.
背景技术Background technique
自蔓延高温合成，是利用化学反应自身放热制备材料的新技术。SHS是20世纪60年代由前苏联发展起来的一种材料合成新方法，其最显著的特点就是充分利用元素间形成化合物时的高能放热反应，除了引发合成反应所必须的少量外加能量，整个反应过程主要依靠物料自身的放热来维持。因此，它可以大大地节省能源。此外，它还具有合成时间短、产物纯度高、污染少、集材料的合成与烧结于一体等突出的优点。Self-propagating high-temperature synthesis is a new technology for preparing materials by exothermic chemical reaction itself. SHS is a new material synthesis method developed by the former Soviet Union in the 1960s. Its most notable feature is to make full use of the high-energy exothermic reaction when forming compounds between elements. In addition to the small amount of external energy necessary to initiate the synthesis reaction, the entire The reaction process is mainly maintained by the heat release of the material itself. Therefore, it can greatly save energy. In addition, it also has outstanding advantages such as short synthesis time, high product purity, less pollution, and integration of material synthesis and sintering.
NiTi合金是一种形状记忆合金，可以应用在包括机器人技术、医疗器械和生物医学植入材料等不同方面。NiTi合金具有强度高、比重低、耐疲劳、耐腐蚀、耐磨损、低磁性、无毒等优点；同时，NiTi合金还具有优良的生物相容性，尤其多孔NiTi合金易于被人体组织固定，是较理想的生物医学植入材料，在医用领域具有广阔的应用前景。NiTi alloy is a shape memory alloy that can be used in different aspects including robotics, medical devices and biomedical implant materials. NiTi alloy has the advantages of high strength, low specific gravity, fatigue resistance, corrosion resistance, wear resistance, low magnetism, and non-toxicity; at the same time, NiTi alloy also has excellent biocompatibility, especially porous NiTi alloy is easy to be fixed by human tissue, It is an ideal biomedical implant material and has broad application prospects in the medical field.
美国1999年专利No.5,986,169中提到，按照1986年俄罗斯出版的由Gunther V.等编写的《医用形状记忆合金》第205页所描述的制备方法可以制备NiTi多孔体合金，特别指出应用SHS方法，即利用层状燃烧过程中Ti、Ni反应所释放的热量合成NiTi合金。所制备的NiTi合金多孔体的成分为40～60wt％Ti(wt％为重量百分比)和60～40wt％Ni，孔隙度为8～90％，实际应用中孔隙度控制在40～80％较好。另外所制备的多孔材料为塑性材料，且表现出各向同性的孔洞连通性，孔洞尺寸分布主要为10～1000μm。U.S. Patent No.5,986,169 in 1999 mentions that NiTi porous body alloys can be prepared according to the preparation method described on page 205 of "Medical Shape Memory Alloys" written by Gunther V. et al. published in Russia in 1986, especially pointing out the application of the SHS method , that is, the NiTi alloy is synthesized by using the heat released by the reaction of Ti and Ni during the layered combustion process. The composition of the prepared NiTi alloy porous body is 40-60wt% Ti (wt% is weight percentage) and 60-40wt% Ni, and the porosity is 8-90%. In practical application, the porosity should be controlled at 40-80%. . In addition, the prepared porous material is a plastic material, and exhibits isotropic pore connectivity, and the pore size distribution is mainly 10-1000 μm.
中国科学院金属研究所李丙运博士于2000年博士论文中提到，将15.2～67.2μm的Ti粉与18.0μm的Ni粉混合后，单向压制成型为Φ33×80mm2的生坯，以氩气作为保护气氛，在自行设计的自蔓延高温合成反应室中，利用自蔓延高温合成方法成功地制备出孔隙度为60Vol.％左右(Vol.％为体积百分比)，开孔率85％以上，孔隙大小为320-510μm的多孔Ni-Ti形状记忆合金。自蔓延高温合成多孔Ni-Ti形状记忆合金的反应完全，形成100％的Ni-Ti金属间化合物。合金中以NiTi相为主，并可观察到少量富Ti或富Ni相。所合成的多孔Ni-Ti形状记忆合金压缩时的屈服强度在9.7～51.4MPa之间，最大可压缩应变量在1.0～3.4％之间；相应的拉伸断裂应力在8.3～18.6MPa之间，延伸率为0.22～0.42％。所制备多孔Ni-Ti形状记忆合金的孔隙尺寸可以满足一般骨组织长入的要求，杨氏模量与网状骨组织的杨氏模量接近，能满足骨骼的强度要求。Dr. Li Bingyun from the Institute of Metal Research, Chinese Academy of Sciences mentioned in his doctoral dissertation in 2000 that after mixing Ti powder of 15.2-67.2 μm and Ni powder of 18.0 μm, they were unidirectionally pressed into a green body of Φ33×80mm 2 and argon was used as the Protective atmosphere, in self-designed self-propagating high-temperature synthesis reaction chamber, using self-propagating high-temperature synthesis method to successfully prepare porosity of about 60Vol.% (Vol.% is volume percentage), open porosity of more than 85%, pore size Porous Ni-Ti shape memory alloy of 320-510μm. The reaction of self-propagating high-temperature synthesis of porous Ni-Ti shape memory alloy is complete, and 100% Ni-Ti intermetallic compound is formed. The alloy is dominated by NiTi phase, and a small amount of Ti-rich or Ni-rich phase can be observed. The yield strength of the synthesized porous Ni-Ti shape memory alloy under compression is between 9.7 and 51.4 MPa, and the maximum compressible strain is between 1.0 and 3.4%; the corresponding tensile fracture stress is between 8.3 and 18.6 MPa, The elongation is 0.22 to 0.42%. The pore size of the prepared porous Ni-Ti shape memory alloy can meet the requirements of general bone tissue ingrowth, and the Young's modulus is close to that of reticular bone tissue, which can meet the strength requirements of bones.
金属注射成形技术(MIM)由陶瓷零件的粉末注射成形技术发展而来，产生于20世纪20年代后期，Schwartzwalder曾发表了几张由金属注射成形技术制取的陶瓷零件的早期照片。近几十年来，MIM技术发展势头迅猛，能应用的材料体系包括：Fe-Ni合金、不锈钢、工具钢、高比重合金、硬质合金、钛合金、镍基超合金、金属间化合物、氧化铝、氧化锆等。经过20多年的努力，目前MIM已成为国际粉末冶金领域发展迅速、最有前途的一种新型近净成形技术，被誉为“国际最热门的金属零部件成形技术”之一。MIM技术的主要生产步骤如下：Metal Injection Molding (MIM) was developed from the powder injection molding technology of ceramic parts and was produced in the late 1920s. Schwartzwalder has published several early photos of ceramic parts made by metal injection molding technology. In recent decades, MIM technology has developed rapidly, and the applicable material systems include: Fe-Ni alloys, stainless steel, tool steel, high specific gravity alloys, hard alloys, titanium alloys, nickel-based superalloys, intermetallic compounds, alumina , Zirconia, etc. After more than 20 years of hard work, MIM has become a rapidly developing and most promising new near-net forming technology in the international powder metallurgy field, and is known as one of the "most popular metal parts forming technologies in the world". The main production steps of MIM technology are as follows:
金属粉末与粘结剂混合后制粒，然后注射成形，再脱脂，然后烧结，再进行后续处理，得到最终产品。The metal powder is mixed with a binder and granulated, then injection molded, then degreased, then sintered, and then processed to obtain the final product.
该技术适用于大批量生产性能高、形状复杂的小尺寸的粉末冶金零部件。目前注射成形技术在国外已经有不少大规模的产业化应用，如瑞士的手表业。而国内近年来也已经涌现出不少具有一定实力MIM产品的生产企业。This technology is suitable for mass production of small-sized powder metallurgy parts with high performance and complex shapes. At present, injection molding technology has many large-scale industrial applications abroad, such as the watch industry in Switzerland. In recent years, many manufacturers of MIM products with certain strengths have emerged in China.
将金属注射成形与自蔓延高温合成相结合制取NiTi合金多孔体，就是以注射成形方法使Ni-Ti混合金属粉得到最终产品的形状及孔隙度。由注射成形坯件发生自蔓延高温合成反应，最终制成多孔NiTi合金材料。将这两种方法相结合制取NiTi合金多孔体主要是因为在注射过程中需加入一定量的粘结剂，经过脱脂后，原来粘结剂存在的位置成为固有的孔隙，有助于SHS制备NiTi多孔体。利用MIM-SHS的另外一个好处就是可以制成形状复杂的零件。Combining metal injection molding with self-propagating high-temperature synthesis to prepare NiTi alloy porous body is to make Ni-Ti mixed metal powder obtain the shape and porosity of the final product by injection molding. A self-propagating high-temperature synthesis reaction occurs from an injection-molded blank, and a porous NiTi alloy material is finally made. Combining these two methods to produce NiTi alloy porous body is mainly because a certain amount of binder needs to be added during the injection process. After degreasing, the original position of the binder becomes an inherent pore, which is helpful for the preparation of SHS. NiTi porous body. Another advantage of using MIM-SHS is that it can make parts with complex shapes.
发明内容Contents of the invention
本发明提供了一种金属注射成形与自蔓延高温合成相结合制取NiTi多孔体材料的方法，解决了复杂形状的成形问题。The invention provides a method for preparing NiTi porous body material by combining metal injection molding and self-propagating high-temperature synthesis, which solves the problem of forming complex shapes.
采用Ti粉和Ni粉作为原材料，按照40～60at％Ti称量(at％为原子百分比)，然后放入球磨罐中，球磨2～36小时后将原材料粉混合均匀。将混合均匀的Ti、Ni混合粉烘干，选择石蜡基粘结剂，按照金属粉体积占50～70％将金属粉和粘结剂在混炼机上进行混炼，混炼温度为110～180℃，然后制粒成为注射用喂料。Ti powder and Ni powder are used as raw materials, weighed according to 40-60 at% Ti (at% is an atomic percentage), and then put into a ball mill jar, and the raw material powders are mixed evenly after ball milling for 2-36 hours. Dry the uniformly mixed Ti and Ni mixed powder, select a paraffin-based binder, and mix the metal powder and the binder on a mixer according to the volume of the metal powder accounting for 50-70%, and the mixing temperature is 110-180 ℃, and then granulated into feed for injection.
将喂料在注射成形机上进行注射成形，注射温度为120～200℃，得到具有一定形状的注射坯件。The feed material is injection-molded on an injection molding machine, and the injection temperature is 120-200°C to obtain an injection blank with a certain shape.
将注射坯件浸入汽油等有机溶剂中进行溶剂脱脂，然后将溶剂脱脂后的坯件晾干，在真空炉里进行热脱脂，热脱脂温度为350～800℃，最后将坯件一端与点火装置的W丝相连接，放入真空反应合成器中，待真空度高于1×10-2pa时开始升温，预热温度范围是150～600℃，达到设定温度后启动点火装置，引燃坯件，即可发生自蔓延高温合成反应，得到产品。Immerse the injection blank in an organic solvent such as gasoline for solvent degreasing, then dry the blank after solvent degreasing, and perform thermal degreasing in a vacuum furnace. The W wires are connected with each other and placed in a vacuum reaction synthesizer. When the vacuum degree is higher than 1×10 -2 pa, the temperature starts to rise. The preheating temperature range is 150-600°C. After reaching the set temperature, start the ignition device to ignite The blank can undergo a self-propagating high-temperature synthesis reaction to obtain a product.
本发明的优点在于：所制备的NiTi合金多孔体孔隙度为40～60％，开孔率可达85％以上，孔洞尺寸约为10～400μm。所合成的多孔NiTi形状记忆合金压缩时的屈服强度在85.5～21.0MPa之间，最大可压缩应变量在1.7～3.6％之间；相应的拉伸断裂应力在21.3～78.5MPa之间，延伸率为3.0～6.7％。所制备多孔Ni-Ti形状记忆合金的孔隙尺寸可以满足一般骨组织长入的要求，杨氏模量为4～8Gpa，与网状骨组织的杨氏模量接近，能满足骨骼的强度要求。The invention has the advantages that: the porosity of the prepared NiTi alloy porous body is 40-60%, the porosity can reach more than 85%, and the pore size is about 10-400μm. The yield strength of the synthesized porous NiTi shape memory alloy in compression is between 85.5-21.0MPa, the maximum compressible strain is between 1.7-3.6%; the corresponding tensile fracture stress is between 21.3-78.5MPa, and the elongation 3.0 to 6.7%. The pore size of the prepared porous Ni-Ti shape memory alloy can meet the requirements of general bone tissue ingrowth, and the Young's modulus is 4-8Gpa, which is close to the Young's modulus of reticular bone tissue, which can meet the strength requirements of bones.
附图说明Description of drawings
图1为本发明制备的NiTi合金多孔体(实施例1)扫描电镜(SEM)照片Fig. 1 is the scanning electron microscope (SEM) photo of NiTi alloy porous body (embodiment 1) prepared by the present invention
图2为本发明制备的NiTi合金多孔体(实施例2)扫描电镜(SEM)照片Fig. 2 is the scanning electron microscope (SEM) photograph of NiTi alloy porous body (embodiment 2) prepared by the present invention
具体实施方式Detailed ways
实施例1Example 1
采用10～100μm Ti粉和10～100μmNi粉作为原材料，按照Ti、Ni原子比1∶1(质量比44.93∶55.07)称量，然后放入球磨罐中，并放入直径5～20mm的不锈钢球(球料比大约为1∶1)用于混料，在球磨机上干混2小时将原材料粉混合均匀。Use 10-100μm Ti powder and 10-100μm Ni powder as raw materials, weigh them according to the atomic ratio of Ti and Ni 1:1 (mass ratio 44.93:55.07), then put them into a ball mill jar and put stainless steel balls with a diameter of 5-20mm (The ratio of ball to material is about 1:1) For mixing, dry mix on a ball mill for 2 hours to mix the raw material powder evenly.
选择石蜡基粘结剂，按照金属粉体积占55％将金属粉和粘结剂在混炼机上进行混炼，混炼温度为135℃，然后破碎为注射用喂料。A paraffin-based binder is selected, and the metal powder and the binder are mixed on a mixer according to the volume of the metal powder accounting for 55%, and the mixing temperature is 135° C., and then crushed into feed for injection.
将喂料在注射成形机上进行注射成形，注射温度为145℃，得到Φ7×120mm2长圆柱形状的注射坯件。The feed material is injection-molded on an injection molding machine at an injection temperature of 145° C. to obtain an injection blank in the shape of a Φ7×120 mm 2 long cylinder.
将注射坯件浸入汽油中进行溶剂脱脂，脱脂时间为24小时。然后将溶剂脱脂后的坯件烘干，在真空度高于1×10-2pa的真空炉里进行热脱脂，热脱脂温度为600℃，保温30min。冷却后将热脱脂的坯件取出，坯件一端与点火装置的W丝相连接，放入真空反应合成器中抽真空，待真空度高于1×10-2pa时开始升温，预热温度为400℃，达到设定温度后启动点火装置，由W丝引燃坯件，即可发生自蔓延高温合成反应，得到产品。The injection blank is immersed in gasoline for solvent degreasing, and the degreasing time is 24 hours. Then dry the blank after solvent degreasing, and perform thermal degreasing in a vacuum furnace with a vacuum degree higher than 1×10 -2 Pa. The thermal degreasing temperature is 600°C and the temperature is kept for 30 minutes. After cooling, take out the thermally degreased blank, connect one end of the blank to the W wire of the ignition device, put it into a vacuum reaction synthesizer to evacuate, and start heating up when the vacuum degree is higher than 1×10 -2 Pa, the preheating temperature The temperature is 400°C. When the set temperature is reached, the ignition device is started, and the blank is ignited by the W wire, and a self-propagating high-temperature synthesis reaction can occur to obtain the product.
由这种工艺制备的NiTi合金多孔体孔隙度为41.9％，开孔率为92.8％；压缩时抗压强度为321.0MPa，可压缩应变量为3.58％；相应的拉伸断裂应力为24.1MPa，延伸率为3.0％，弹性模量为6.0Gpa。The NiTi alloy porous body prepared by this process has a porosity of 41.9%, an open porosity of 92.8%, a compressive strength of 321.0MPa, and a compressible strain of 3.58%. The corresponding tensile fracture stress is 24.1MPa, The elongation is 3.0%, and the modulus of elasticity is 6.0Gpa.
这种工艺所制备的NiTi合金多孔体SEM照片见图1。The SEM photo of the NiTi alloy porous body prepared by this process is shown in Fig. 1 .
实施例2Example 2
其操作方法和工艺条件基本同实施例1，唯一不同的是在发生自蔓延高温合成反应前的预热温度为500℃。The operation method and process conditions are basically the same as those in Example 1, except that the preheating temperature before the self-propagating high-temperature synthesis reaction is 500°C.
由这种工艺制备的NiTi合金多孔体孔隙度为58.5％，开孔率为91.0％；压缩时抗压强度为107.5MPa，可压缩应变量为2.07％；相应的拉伸断裂应力为78.5MPa，延伸率为6.5％，弹性模量为4.1Gpa。The NiTi alloy porous body prepared by this process has a porosity of 58.5%, an open porosity of 91.0%, a compressive strength of 107.5MPa and a compressible strain of 2.07% when compressed, and a corresponding tensile fracture stress of 78.5MPa, The elongation is 6.5%, and the modulus of elasticity is 4.1Gpa.
这种工艺所制备的NiTi合金多孔体SEM照片见图2。The SEM photo of the NiTi alloy porous body prepared by this process is shown in Fig. 2 .
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