Ti-35Nb-7Zr-10CPP生物复合材料的微观组织演变与力学性能研究

利用放电等离子烧结技术制备了Ti-35Nb-7Zr-10CPP生物复合材料,研究了不同烧结温度(950~1150℃)对复合材料致密度、微观组织演变与力学性能的影响及机理。结果表明,复合材料主要由β-Ti相基体、少量残留α-Ti相及CaTiO_3、Ti_2O、CaO、CaZrO_3、Ti_xP_y等金属-陶瓷相组成;随着烧结温度升高,复合材料中残留α-Ti相逐渐减少,而金属-陶瓷相逐渐增多;复合材料的压缩弹性模量与抗压强度随烧结温度升高呈增大趋势,但是当烧结温度超过1050℃时,由于金属与陶瓷的剧烈反应导致金属-陶瓷相迅速增多,从而使得压缩弹性模量快速增大。因此,当烧结温度在1000~1050℃范围时,复合材料获得了较好的综合力学性能,其压缩弹性模量为42~45 GPa、抗压强度为1240~1330MPa;同时,在模拟人工体液中浸泡7 d后,复合材料表面能够获得一层致密的类骨磷灰石层,显示了良好的生物活性。     

放电等离子烧结Ti-35Nb-7Zr-xHA复合材料的力学性能与腐蚀性能（英文）

为了改善Ti-Nb-Zr合金的生物活性,采用放电等离子烧结(SPS)制备了Ti-35Nb-7Zr-xHA(羟基磷灰石,x=5,10,15,20,质量分数,%)复合材料。借助XRD、SEM、力学测试以及电化学测试手段研究了HA含量对复合材料显微组织、力学性能和腐蚀性能。结果表明,所有复合材料的物相主要由β-Ti基体、α-Ti和金属-陶瓷相(CaO,CaTiO_3,CaZrO_3,TixPy等)组成,此外,含15%HA和20%HA的复合材料中出现了少量残余的HA;随着HA含量的增加,复合材料的抗压强度均高于1400MPa,复合材料(5%-15%HA)的弹性模量呈较小变化趋势(46-52GPa),更加接近人骨的弹性模量。在Hank’s溶液中的电化学试验表明,HA含量为15%时,复合材料的钝化电流密度和腐蚀电流密度较低,显示了较好的腐蚀性能。因此,Ti-35Nb-7Zr-15HA复合材料可作为一种骨科植入手术中较好的替代材料。     

放电等离子烧结温度对Ti-35Nb-7Zr-5Ta合金显微组织和力学性能的影响

利用放电等离子烧结技术(SPS)制备了Ti-35Nb-7Zr-5Ta合金,研究了烧结温度对合金致密度、显微组织及力学性能的影响。结果表明:在950~1150℃烧结温度范围内合金主要由β-Ti相和Ti-Nb-Ta-Zr固溶体组成的混合基体及少量未熔化的Nb、Ta金属颗粒组成,并且合金具有较高的致密度和抗压强度;随着烧结温度的升高,合金中混合基体组织尺寸越来越大且不断融合联结,Nb、Ta金属颗粒数量越来越少且尺寸越来越小,同时合金致密度和抗压强度呈增大趋势;所制备的合金压缩弹性模量值在50~57 GPa之间,具有良好的力学相容性,烧结温度变化对其影响较小。     

烧结温度对SPS制备Ti-24Nb-4Zr-8Sn合金组织和力学性能的影响

利用放电等离子烧结技术(SPS)制备了Ti-24Nb-4Zr-8Sn合金,研究了烧结温度对合金相对密度、显微组织及力学性能的影响。结果表明:在1000~1200℃烧结温度范围内合金具有较高的相对密度和抗压强度,合金主要由β-Ti相和Ti-Nb固溶体组成的混合基体及少量α-Ti相组成;随着烧结温度的升高,合金相对密度和抗压强度呈增大趋势,合金中α-Ti相向β-Ti相逐渐转变,同时合金中Ti-Nb固溶体含量越来越少,且尺寸减小;合金压缩弹性模量在58~61 GPa之间,受烧结温度变化影响较小。     

退火温度对HA/Ti-24Nb-4Zr复合材料组织与性能的影响

利用放电等离子烧结(SPS)技术制备了HA/Ti-24Nb-4Zr生物复合材料,研究了不同退火温度对复合材料显微组织和力学性能(抗压强度、屈服强度、屈强比、压缩弹性模量)的影响。结果表明,烧结态复合材料主要由β-Ti相、少量初生α-Ti相及HA相组成;随着退火温度的升高,复合材料基体中β-Ti相含量增多且晶粒逐渐长大,针状次生α-Ti相在晶界处和晶内不断析出,HA相结构和含量变化不大;与烧结态相比,不同退火温度处理后的复合材料强度和弹性模量先略微上升后下降,而塑韧性呈不断提高趋势;复合材料在850 ℃退火处理后,抗压强度、屈服强度、屈强比和压缩弹性模量值分别为1507 MPa、1270 MPa、0.84和42 GPa,塑韧性得到明显改善,作为生物医用植入材料具有潜在的应用前景。     

放电等离子烧结温度对Ti-29Nb-13Ta-4.6Zr合金显微组织和力学性能的影响

利用放电等离子烧结技术(SPS)制备Ti-29Nb-13Ta-4.6Zr(TNTZ)合金,研究烧结温度对合金致密度、显微组织及力学性能的影响。结果表明:在950~1150℃烧结温度范围内合金具有较高的致密度和抗压强度,合金由β-Ti相与Ti-Nb-Ta-Zr固溶体形成的混合基体组织及少量未熔化的Nb、Ta、Zr金属颗粒组成。随着烧结温度的升高,合金致密度和抗压强度呈增大趋势,合金中混合基体组织尺寸越来越大且不断融合联结,难熔金属颗粒数量越来越少且尺寸越来越小。合金压缩弹性模量在58~60GPa之间,说明具有良好的力学相容性,烧结温度变化对其影响较小。     

烧结温度对Sr掺杂HA/Ti复合材料组织结构及体外生物活性的影响

采用溶胶凝胶法制备了锶掺杂羟基磷灰石(Sr-HA)粉末,将制备的Sr-HA粉末和Ti粉按质量比2∶8压制成坯,在大气环境下烧结制备Sr-HA/Ti生物复合材料,研究烧结温度对Sr-HA/Ti生物复合材料组织结构及生物活性的影响。结果表明:烧结后Sr-HA/Ti复合材料主要由Sr-HA、Ti、TiO₂、CaO等物相组成,当温度达到950 ℃时,材料表面氧化严重,Sr-HA分解增加。大气条件下烧结制备的Sr-HA/Ti复合材料孔径可以满足骨组织长入基本要求,烧结后复合材料冶金结合良好,随着烧结温度的提高复合材料表面孔隙数量增多,孔隙直径减小,细小的孔隙均匀分布于TiO₂及α-Ti形成网格结构之间。模拟体液浸泡14天后,850 ℃烧结的试样表面陶瓷相沉积效果最好,复合材料表面生成了利于成骨的Ca₅(PO₄)_3-x(CO₃)_xOH相。     

Ti-35Nb-7Zr-XCPP生物复合材料的放电等离子烧结制备及其力学性能研究

采用放电等离子烧结技术制备了Ti-35Nb-7Zr-XCPP生物复合材料,研究了焦磷酸钙(CPP)含量对复合材料致密度、微观结构、显微组织及其力学性能(压缩强度、压缩弹性模量)的影响。结果表明:复合材料组织主要由β-Ti相基体、少量残留α-Ti相及CPP相组成,CPP含量的增加会导致复合材料中残留α-Ti相含量增加,过高的CPP加入量会使得CPP发生分解现象;复合材料具有较低的压缩弹性模量(40~62 GPa)和较高的抗压强度(1000 MPa以上),显示了良好的力学相容性,过高的CPP加入量会导致复合材料压缩弹性模量出现明显增大现象,从而对复合材料力学相容性产生不利的影响。     

Ti-13Nb-13Zr表面多孔梯度合金的制备及性能研究

利用放电等离子烧结（SPS）技术制备了中间致密、表面多孔的Ti-13Nb-13Zr梯度合金,研究了烧结温度（950~1200 ℃）对梯度合金组织演变、界面结合、表面孔隙特征、力学及体外矿化性能的影响。结果表明：随烧结温度的逐步上升,梯度合金中α-Ti相减少,β-Ti相增多,组织逐渐连续均匀分布,晶粒得到细化,中间基体与多孔层界面呈连续过渡且形成良好的冶金结合,表面多孔层孔隙率下降而平均孔径减小;梯度合金抗压强度值随烧结温度升高呈先增大后降低趋势,而弹性模量值变化不大;综合分析,烧结温度为1150 ℃时,制备的表面多孔梯度合金不仅具有良好的力学性能（抗压强度893MPa,弹性模量16GPa）,而且具有适宜的孔隙参数（孔隙率34.7%,平均孔径340.9μm）及优异的类骨磷灰石形成能力与体外矿化性能。     

粉末冶金制备TNZS基生物材料的组成、结构和性能

采用高能球磨48 h制备Ti-24Nb-4Zr-7.9Sn(TNZS)、5%TiO_2/TNZS及5%HA/TNZS混合粉末(质量分数,下同)并进行冷压烧结,研究了3种混合粉末的形貌、物相及冷压烧结后3种TNZS基生物材料的组织、成分、相组成、孔隙特征及弹性模量。高能球磨48 h的3种混合粉末都发生机械合金化;烧结后TNZS相组成为α-Ti和β-Ti,5%TiO_2/TNZS相组成为α-Ti、β-Ti、金红石TiO_2和锐钛矿TiO_2,5%HA/TNZS相组成除α-Ti、β-Ti、HA外,还有Ti_2O、Ca TiO_3、CaO和TixPy新相生成;三者孔隙率分别为2.466%、5.030%和13.027%;三者弹性模量分别为64.00、103.93和119.43 GPa。     

Characterizations on Mechanical Properties and In Vitro Bioactivity of Biomedical Ti–Nb–Zr–CPP Composites Fabricated by Spark Plasma Sintering

To alleviate the bio-inert of Ti alloys as hard tissue implants, Ti–35Nb–7Zr–xCPP(calcium pyrophosphate,x = 5, 10, 15, 20 wt%) composites were prepared by mechanical alloying(MA) and following spark plasma sintering(SPS). Mechanical behaviours and in vitro bioactivity of these composites were investigated systematically. Results showed that the composites consisted of β-Ti matrix, α-Ti, and metal–ceramic phases such as CaO, CaTiO_3, CaZrO_3, and Ti_xP_y. With increasing CPP content, the composites had higher strength(over 1500 MPa) and higher elastic modulus, but suffered almost zero plastic deformation together with lower relative density. When the CPP contents were 5 and 10 wt%,the compressive elastic moduli were 44 and 48 GPa, respectively, which were close to those of natural bones. However, the compressive elastic modulus of the composites increased significantly when CPP contents exceed 10 wt%, thus deteriorating the mechanical compatibility of the composites owing to more α-Ti and metal–ceramic phases. Besides, the surface of Ti–35Nb–7Zr–10CPP composite was deposited as a homogeneous apatite layer during soaking in simulated body fluid(SBF). It indicates a good bioactivity between the implant materials and living bones.     

Mechanical and corrosion properties of Ti-35Nb-7Zr-xHA composites fabricated by spark plasma sintering

To improve the bioactivity of Ti-Nb-Zr alloy, Ti-35Nb-7Zr-xHA (hydroxyapatite, x=5, 10, 15 and 20, mass fraction, %) composites were fabricated by spark plasma sintering. The effects of the HA content on microstructure, mechanical and corrosion properties of the composites were investigated utilizing X-ray diffraction (XRD), scanning electron microscope (SEM), mechanical tests and electrochemical tests. Results show that all sintered composites are mainly composed of β-Ti matrix, α-Ti and metal–ceramic phases (CaO, CaTiO₃, CaZrO₃, Ti_xP_y, etc). Besides, some residual hydroxyapatites emerge in the composites (15% and 20% HA). The compressive strengths of the composites are over 1400 MPa and the elastic moduli of composites ((5%–15%) HA) present appropriate values (46–52 GPa) close to that of human bones. The composite with 15% HA exhibits low corrosion current density and passive current density in Hank's solution by electrochemical test, indicating good corrosion properties. Therefore, Ti-35Nb-7Zr-15HA composite might be an alternative material for orthopedic implant applications.     

Characterization of the Ti-10Nb-10Zr-5Ta Alloy for Biomedical Applications. Part 1: Microstructure, Mechanical Properties, and Corrosion Resistance

Ti-10Nb-10Zr-5Ta alloy was investigated as possible material candidate for replacing Ti6Al4V in medical applications. The alloy was prepared in a levitation melting furnace and characterized in terms of elemental and phase composition, microstructure, mechanical properties, and corrosion resistance in simulated body fluid and Fusayama Meyer artificial saliva solutions. The characteristics of the new alloy were compared to those of the Ti6Al4V alloy. The Ti-10Nb-10Zr-5Ta system was found to posses of a polyhedral structure consisting in α′ and β phases. X-ray structural analysis revealed a mixture of hexagonal α′ martensite (main phase, with grain size of about 21 nm) and β bcc phase. The Ti-10Nb-10Zr-5Ta alloy exhibited some better mechanical properties (Young modulus, tensile properties) and corrosion resistance (polarization resistance, corrosion current density, and corrosion rate), as compared to Ti6Al4V alloy.     

Characterization of the Ti-10Nb-10Zr-5Ta Alloy for Biomedical Applications. Part 2: Wettability, Tribological Performance and Biocompatibility

The Ti-10Nb-10Zr-5Ta alloy, prepared in a levitation melting furnace, was investigated as a possible candidate for replacing Ti6Al4V alloy in medical applications. The sessile drop method, pin-on-disc and in vitro tests were used to analyze wettability, wear resistance, and biocompatibility of the new alloy. The characteristics of the Ti-10Nb-10Zr-5Ta alloy were assessed in comparison to those of the Ti6Al4V alloy. The Ti-10Nb-10Zr-5Ta system was found to have hydrophilic characteristics with similar contact angle as the Ti6Al4V alloy. In all environments (deionized water, simulated body fluid and Fusayama Meyer artificial saliva), the friction coefficient showed a stable evolution versus sliding distance, being similar for both alloys. On overall, the wear resistance of Ti-10Nb-10Zr-5Ta alloy was lower than that of Ti6Al4V for all testing environments. The Ti-10Nb-10Zr-5Ta alloy exhibited good biocompatibility characteristics at in vitro test compared to Ti6Al4V alloy. The cell viability on Ti-10Nb-10Zr-5Ta surfaces was higher than the one observed on Ti6Al4V samples, regardless the number of days spent in osteoblast-like cells culture. A high degree of cell attachment and spreading was observed on both alloys.     

生物医用钛合金的研究进展

钛合金具有较低的弹性模量、优异的耐腐蚀性能和生物相容性,是理想的生物医用材料.综述了医用钛合金的发展过程及新型医用β钛合金的研究现状,以及开发的新合金系列.目前开发的医用钛合金中,Ti-35Nb-7Zr-5Ta和Ti-29Nb-13Ta-7.1Zr合金的弹性模量为55 GPa,与致密骨的弹性模量很接近,与人体骨有较好的...     

Microstructure, mechanical, and anticorrosive properties of a new Ti-20Nb-10Zr-5Ta alloy based on nontoxic and nonallergenic elements

For an alloy to be suitable for use as an implant material, it must have a low specific weight and Young??s modulus, good mechanical properties that are similar to those of bone, and very good corrosion resistance and biocompatibility. In this study, we have developed a novel Ti-20Nb-10Zr-5Ta alloy that is composed of nontoxic, nonallergenic, corrosion-resistant elements. This alloy has low specific weight and Young??s modulus and good mechanical properties. It has a fine microstructure with a matrix that is mainly composed of the ?? phase and some ?? phase due to recrystallization during cooling. It shows elastoplastic behavior with a fairly linear elastic behavior and low Young??s modulus (59 GPa). In addition, its ultimate tensile strength, 0.2% yield strength, and hardness are higher than those of CP Ti, commercial Ti-6Al-4V, and similar ??-type alloys. It exhibited a very stable passive state and its electrochemical parameters and corrosion and ion release rates were better than those of CP Ti in Ringer??s solutions of different pH values that simulate the severe functional conditions of an implant; this is attributable to the beneficial influence of the alloying elements and to the better protective properties of the coated passive film.     

Ta含量对Ti-6Al-3Nb-2Zr-1Mo-xTa合金力学性能和腐蚀性能的影响

系统研究了Ti-6Al-3Nb-2Zr-1Mo-x Ta(x=0,0.2,0.5,1.0,3.0,5.0)合金的微观组织、拉伸性能、夏比冲击韧性和耐海水腐蚀性。结果表明,经α+β两相区锻造后,Ti-6Al-3Nb-2Zr-1Mo-5Ta合金获得片层组织,Ti-6Al-3Nb-2Zr-1Mo-x Ta(x=0,0.2,0.5,1.0,3.0)均获得双态组织。XRD、TEM和选区电子衍射表明,在添加Ta元素后,Ti-6Al-3Nb-2Zr-1Mo-x Ta合金没有新相产生。对于双态组织Ti-6Al-3Nb-Zr-1M0-x Ta合金,随着Ta含量的增加,其Mo当量逐渐增加,导致其屈服强度、抗拉强度和显微硬度均有所提高。而Ta含量对冲击吸收功的影响规律与屈服强度和抗拉强度的影响规律相反,其大小与冲击断口剪切唇区面积一致。当Ta含量超过1.0%(质量分数)时,由于α和β相之间的标准平衡电位差逐渐增大,Ti-6Al-3Nb-2Zr-1Mo-x Ta合金的耐海水腐蚀逐渐降低。综合考虑强度、冲击韧性和耐海水腐蚀性能,Ti-6Al-3Nb-2Zr-1Mo-1Ta合金综合匹配性最好,具有良好的海洋工程应用潜力。     

球磨时间对粉末冶金制备Ti35Nb2.5Sn/10HA生物复合材料微观组织的影响(英文)

采用高能机械球磨和脉冲电流活化烧结方法制备了一种新型的β-钛合金基体的Ti35Nb2.5Sn/10HA生物复合材料。研究了机械球磨不同时间的Ti35Nb2.5Sn10HA粉体以及烧结样品的微观组织。结果表明:经机械球磨8h后,粉体中的α-钛开始向β-钛转化。当球磨时间达到12h时,球磨粉体中的α-钛相完全转化为β-钛相,而且得到超细尺寸的复合粉体。用球磨12h的粉末烧结制备的复合材料具有超细晶粒结构,烧结得到的复合材料的硬度和相对密度都随着球磨时间的延长而增加。     

Effect of brazing temperature and brazing time on the microstructure and tensile strength of TiAl-based alloy joints with Ti-Zr-Cu-Ni amorphous alloy as filler metal

An amorphous Ti-37.5Zr-15Cu-15Ni (wt.%) ribbon fabricated by vacuum arc remelting and rapid solidification was used as filler metal to vacuum braze TiAl alloy (Ti-45Al-2Mn-2Nb-1B (at.%)). The effects of brazing temperature and time on the microstructure and strength of the joints were investigated in details. The typical brazed joint major consisted of three zones and the brazed joints mainly consisted of α_2-Ti₃Al phase, α-Ti phase and (Ti, Zr)₂(Cu, Ni) phase. When the brazing temperature varied from 910 °C to 1010 °C for 30 min, the tensile strength of the joint first increased and then decreased. With increasing the brazing time, the tensile strength of the joint increased. The maximum room temperature tensile strength was 468 MPa when the specimen was brazed at 930 °C for 60 min. All the fracture surfaces assumed typical brittle cleavage fracture characteristic. The fracture path varied with the brazing parameter and cracks preferred to initiate at (Ti, Zr)₂(Cu, Ni) phase and propagation path were mainly determined by the content and distribution of α-Ti phase and (Ti, Zr)₂(Cu, Ni) phase.