Representative microstructures of several Zn-based alloys under different processing conditions: (a) Zn-Mg, (b) Zn-Cu, (c) Zn-Mn: tensile twinning is highlighted in red, (d) Zn-Al: white and red arrows represent Zn + Mg 2 Zn 11 eutectic and b(Zn) + a(Al) monotectoid constituents, respectively, (e) Zn-Cu-Mg, (f) Zn-Li, (g) Zn-Ag. All compositions are given in wt%. Adapted with permission from [23,79,84,88,91,92]. (For interpretation of the references to color in this figure legend, the reader is referred to the web version of this article.)

Representative microstructures of several Zn-based alloys under different processing conditions: (a) Zn-Mg, (b) Zn-Cu, (c) Zn-Mn: tensile twinning is highlighted in red, (d) Zn-Al: white and red arrows represent Zn + Mg 2 Zn 11 eutectic and b(Zn) + a(Al) monotectoid constituents, respectively, (e) Zn-Cu-Mg, (f) Zn-Li, (g) Zn-Ag. All compositions are given in wt%. Adapted with permission from [23,79,84,88,91,92]. (For interpretation of the references to color in this figure legend, the reader is referred to the web version of this article.)

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Absorbable metals have the potential to serve as the next generation of temporary medical implant devices by safely dissolving in the human body upon vascular tissue healing and bone regeneration. Their implementation in the market could greatly reduce the need of costly and risky additional surgeries for either implant replacement or removal, ofte...

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... to obtain stent-sized mini tubes. In agreement with the Zn-Mg phase diagram, the microstructures of hypoeutectic Zn-0.15Mg, Zn-0.5Mg and Zn-1Mg consisted of Zn dendritic grains embedded in a eutectic matrix of Zn and Mg 2 Zn 11 . In contrast, Zn3Mg exhibited a fully eutectic microstructure with fine alternate lamellae of Zn and Mg 2 Zn 11 (Fig. 4a). In all the alloys, increasing the Mg content decreased the grain size [79]. Jin et al. [64] reached this same conclusion from extruded and drawn Zn-Mg alloys containing 0.08, 0.005 and 0.002 (wt%) ...
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... forms a mixture of Zn and CuZn 5 phases. Zn-xCu (x = 1, 2, 3, 4 wt%) binary alloys were investigated by Tang et al. [84] and Niu et al. [85] for absorbable cardiovascular implants. The as-cast microstructures consisted of dendritic CuZn 5 phase embedded in primary Zn matrix, with an increasing dendritic volume fraction at higher Cu concentrations (Fig. 4b). Homogenization of the alloys at 360 °C did not alter the microstructure, which indicated the thermal stability of the CuZn 5 intermetallic. Further hot-extrusion processing caused grain refinement, especially in the regions closer to the CuZn 5 phase, due to dynamic recrystallization. The effect of small Mg additions to the Zn-Cu ...
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... of small Mg additions to the Zn-Cu system was investigated through a series of Zn-3Cu-xMg (x = 0, 0.1, 0.5, 1.0 wt%) ternary alloys by Tang et al. [86]. Increasing Mg concentration gradually refined the grain size and led to a more homogenous microstructure, containing both the CuZn 5 and Mg 2 Zn 11 phases, in the as-cast and asextruded alloys (Fig. 4e), which resulted in a higher tensile strength and a relatively uniform corrosion behavior. Yue et ...
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... (x = 0.2, 0.4, 0.6 wt%) were studied by Sun et al. [88]. The Zn-0.2Mn alloy showed only Zn-rich phases, whereas the MnZn 13 intermetallic was identified in the Zn-0.4Mn and Zn-0.6Mn alloys. The average grain size of the hot-extruded alloys decreased notably with the addition of 0.2 (wt%) Mn and remained relatively constant with higher Mn content (Fig. 4c). In addition, the twinning volume fraction (highlighted in red in Fig. 4c) decreased gradually with increasing Mn content, while a basal texture was maintained regardless of Mn content. Consequently, dislocation movement was enhanced with higher Mn content resulting in an increase of the e f at the expense of the tensile strength. ...
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... showed only Zn-rich phases, whereas the MnZn 13 intermetallic was identified in the Zn-0.4Mn and Zn-0.6Mn alloys. The average grain size of the hot-extruded alloys decreased notably with the addition of 0.2 (wt%) Mn and remained relatively constant with higher Mn content (Fig. 4c). In addition, the twinning volume fraction (highlighted in red in Fig. 4c) decreased gradually with increasing Mn content, while a basal texture was maintained regardless of Mn content. Consequently, dislocation movement was enhanced with higher Mn content resulting in an increase of the e f at the expense of the tensile strength. Sotoudeh Bagha et al. [89] prepared Zn-xMn (x = 4, 24 wt%) alloys via powder ...
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... The latter is not stable below 275 °C and transforms into a-Al through a monotectoid reaction. Zn-xAl (x = 0.5, 1 wt%) binary alloys were explored by Mostaed et al. [79] for absorbable stent applications. The as-cast microstructures consisted of a Zn matrix with a small content of a Zn-Al eutectoid mixture located mainly at the grain boundaries (Fig. 4d), which act as pinning points and therefore delay grain growth leading to finer grain sizes. Further solution treatment at 350 °C was found to dissolve the eutectic constituent in the Zn-rich matrix, forming a supersaturated solid solution. Despite the toxicity concern of Al, higher Al-containing alloys, such as Zn-xAl (x = 1, 3, 5 ...
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... also been alloyed with Ag, which presents a solubility limit in Zn of about 6 (wt%) at 431 °C, where a peritectic reaction transforms AgZn 3 and liquid into a Zn solid solution (Fig. 3g). Sikora-Jasinska et al. [91] observed that the as-cast microstructure of Zn-xAg (x = 2.5, 5, 7 wt%) alloys consisted of a primary Zn matrix and AgZn 3 dendrites (Fig. 4g), with an increasing volume fraction of the latter at higher Ag contents. After solution treatment at 410 °C, the AgZn 3 dendrites were fragmented into equiaxed particles uniformly dispersed through the Zn matrix. Upon 6 h and 12 h solution treatments for the 2.5-5 and 7 (wt%) Ag alloys, respectively, the AgZn 3 phase was dissolved ...
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... is another element added to Zn, and its maximum solubility in Zn is only about 0.1 wt% at 403 °C (Fig. 3h). At that temperature, a eutectic reaction transforms the liquid phase into Zn and b-LiZn 4 , which further transforms to a-LiZn 4 below 65 °C. (Fig. 4f). After hot rolling, the Zn-0.4Li and Zn-0.7Li alloys exhibited a severe rolling texture with finer dendrites and grains, while Zn-0.2Li presented equiaxed grains due to dynamic recrystallization. ...

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... However, pure Zn fails to meet the clinical application standard because of its low strength and plasticity. To improve its mechanical properties, methods such as alloying and plastic deformation are often used [4,5]. Compared with as-cast pure Zn, the strength of as-cast Zn-based alloys can be significantly improved due to solid solution strengthening and second-phase strengthening. ...
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To investigate the effects of adding trace amounts of Li on the microstructure, mechanical properties, corrosion behavior, antibacterial activity and biocompatibility of the Zn–Cu alloy, Zn–1.2Cu, Zn–1.2Cu–0.02Li as well as Zn–0.02Li (as a reference) alloys were prepared in this work. The results showed that the grain size of the as-cast Zn–1.2Cu–0.02Li alloy is significantly smaller than that of the Zn–1.2Cu alloy, suggesting a notable effect of the trace amounts of Li on the grain refinement. Moreover, a bimodal structure was formed in both the hot-extruded Zn–1.2Cu and Zn–1.2Cu–0.02Li alloys due to the precipitation of submicron-sized ɛ-CuZn4 particles. However, the latter has a much higher volume fraction of submicron-sized ɛ-CuZn4 particles than the former. Furthermore, nano-sized ɛ-CuZn4 particles precipitate from the matrix of the fine-grained region in the latter alloy. The hot-extruded Zn–1.2Cu–0.02Li alloy exhibits a yield strength (YS) of 278 ± 3 MPa and ultimate tensile strength (UTS) of 320 ± 1 MPa, which are 76% and 25% higher than the hot-extruded Zn–1.2Cu alloy (YS = 158 ± 3 MPa and UTS = 225 ± 1 MPa), indicating a strong strengthening effect of trace amounts of Li. Furthermore, the hot-extruded Zn–1.2Cu–0.02Li alloy has a lower corrosion rate than the Zn–1.2Cu alloy, indicating a positive effect of trace amounts of Li on the corrosion resistance. In addition, the hot-extruded Zn–1.2Cu and Zn–1.2Cu–0.02Li alloys both demonstrate hemolysis rates of less than 5% and antibacterial rates of more than 97%, indicating good hemocompatibility and antibacterial property. Also, the MC3T3-E1 cells show over 110% viability in the 50% extracts of both alloys, exhibiting excellent cytocompatibility. Graphical Abstract
... Compared to Mg and Fe, Zn exhibits more biodegradation behavior to match the anatomical requirement. Zn is the second highest trace mineral in the human body which acts to maintain cardiomyopathy cardiac function and for the formation of new bone [94]. The lack of Zn in the human body is linked to the weaknesses and poor health of bone [95]. ...
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... Due to the slow degradation rate of Fe alloys in the early research, Mg alloys and Zn alloys with faster degradation rates have become important materials for developing the degradable anastomotic staples [65]. Nevertheless, the high degradation rate of Mg alloys and the need to improve the strength of Zn alloys still require more explorations for the biodegradable staples by now [69]. Based on the fruitful achievements of biodegradable nitrogen-containing Fe alloys in the cardiovascular field [68], this study firstly evaluated the biocompatibility, degradation and biofunctions of the HN-Fe staples in vivo. ...
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... Biodegradable metals are widely used in clinical operations [3][4][5][6]. Zinc-based alloys are considered potential biodegradable implant materials due to their ideal degradation rate, mild mechanical qualities, and good biocompatibility [7][8][9][10][11]. Furthermore, Zn is an essential element necessary for many metabolic activities. ...
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... Moreover, using zinc as a biodegradable material is an interesting concept, and researchers are exploring strategies to enhance the application and performance of zinc in the context of the implant biodegradability (Kabir et al., 2021). Zinc and its alloys are the most promising biodegradable metallic materials for clinical use (Hernández-Escobar et al., 2019;Zhuo et al., 2022). Research on the possibility of combining and connecting biodegradable zinc with other biocompatible materials, such as stainless steel and titanium, as implant development is very promising, such as implants for external fixation with biodegradable screws. ...
... In recent years, zinc (Zn)-based alloys have shown promise as a biodegradable material in the field of orthopedic implants owing to their advantageous corrosion behavior [15,16]. The osteogenic properties of Zn-based materials have been revealed by the previous studies [17][18][19][20]. ...
... It is acknowledged that Zn serves as a crucial element for the bone metabolism and immune systems. Among the biodegradable metals, Znbased metals are the better candidates in the field of osteosynthesis implants owing to their degradation rate, corrosion products and biocompatibility [15,16]. Nevertheless, the mechanical characteristics of pure Zn cannot meet the requirements in clinic. ...
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... Much previous research has already demonstrated the suitability of Zn alloys for potential use as biodegradable metallic materials. Preliminary in vitro and in vivo results all show that Zn alloys have moderate biodegradation rates and play an important role in promoting new bone formation and remodeling [ 82 ]. The alloying element Mg is an essential element for human bone health. ...
... On the other hand, in recent years, the application of metallic ions in medicine has become a hot research topic in regards to their application as drug release modifiers or antimicrobial agents (Hernández-Escobar et al., 2019;Ramya et al., 2015). If the mechanism of alginate gelation is still explained in terms of the original egg-box model, from monocomplexes to the egg-box dimers, and the laterally associated egg-box multimers (Braccini & Pérez, 2001;Cao, Lu, Mata, Nishinari & Fang, 2020;Mørch, Donati, Strand & Skjåk-Braek, 2007;Fang et al., 2007), some novel insights to the influence of different crosslinking agents have been proposed in particular with a specific focus on the final properties of this hydrogels and their potential application (Donati & Christensen, 2023;Hu, Lu, Mata, Nishinari & Fang, 2021;Tan et al., 2023). ...
... It seems worthwhile to note, that for pure zinc with a melting point of 693 K room temperature already describes a relatively high homologous temperature of 0.42. While the respective property profile of wires will depend on the envisioned application (e.g. as medical application as a biodegradable material) typical properties for stents and bone-fixture devices have been emphasized during reviews of such applications [2,4,25,26]. In this context, the yield stress should exceed 200 MPa or 230 MPa, the tensile strength should exceed 300 MPa in general and the fracture strain as a measure for the ductility of the materials should exceed 15-18 % as benchmark levels. ...
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Zinc (Zn) in particular has gained attention as biodegradable metal due to its advantageous corrosion rates compared to magnesium (Mg) or iron (Fe). Still, strength and ductility of zinc are found to be unfavorable for many medical applications. Strategies to overcome such issues base on a distinct grain refinement of the respective product. One important condition of the metal is assumed to be in the form of wires, which in the present work stem from a direct extrusion setup and high degrees of deformation, therefore a hot forming procedure as the underlying thermomechanical treatment. A basic binary alloying approach with Mg, manganese (Mn) and copper (Cu) is applied, limiting the content to a solid solution range of the alloys. The processability and the processing ranges are examined as well as their impact on the microstructure development and the resulting mechanical behavior. Higher extrusion speed leads to inhomogeneous material flow during extrusion. Alloying Zn can reduce the influence of process parameters and decrease the average grain sizes of wires which experienced lower temperature impact. The forming ability of pure Zn and ZnMg-alloy remain limited whereas they appear more beneficial for the alloys with Mn and especially Cu.
... Sr, a bone-supporting element, has been shown to promote cell differentiation and new bone formation, although the low concentration of Sr 2+ results in a minimal effect on cell activity [12]. Hernandez et al. [57] observed that the Zn alloy exhibits significant cytotoxic effects in vitro, but the toxicity is markedly reduced in vivo. This reduction may be due to protein absorption, body fluid dynamics, and the possibility that degradation products may be recycled and excreted in feces and urine [58]. ...
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In recent years, the use of zinc (Zn) alloys as degradable metal materials has attracted considerable attention in the field of biomedical bone implant materials. This study investigates the fabrication of porous scaffolds using a Zn-1Mg-0.1Sr alloy through a three-dimensional (3D) printing technique, selective laser melting (SLM). The results showed that the porous Zn-1Mg-0.1Sr alloy scaffold featured a microporous structure and exhibited a compressive strength (CS) of 33.71 ± 2.51 MPa, a yield strength (YS) of 27.88 ± 1.58 MPa, and an elastic modulus (E) of 2.3 ± 0.8 GPa. During the immersion experiments, the immersion solution showed a concentration of 2.14 ± 0.82 mg/L for Zn2+ and 0.34 ± 0.14 mg/L for Sr2+, with an average pH of 7.61 ± 0.09. The porous Zn-1Mg-0.1Sr alloy demonstrated a weight loss of 12.82 ± 0.55% and a corrosion degradation rate of 0.36 ± 0.01 mm/year in 14 days. The Cell Counting Kit-8 (CCK-8) assay was used to check the viability of the cells. The results showed that the 10% and 20% extracts significantly increased the activity of osteoblast precursor cells (MC3T3-E1), with a cytotoxicity grade of 0, which indicates safety and non-toxicity. In summary, the porous Zn-1Mg-0.1Sr alloy scaffold exhibits outstanding mechanical properties, an appropriate degradation rate, and favorable biosafety, making it an ideal candidate for degradable metal bone implants.