A study on the mechanical characteristics of the EBM-printed Ti-6Al-4V LCP plates in vitro
© Liu et al.; licensee BioMed Central Ltd. 2014
Received: 8 October 2014
Accepted: 21 October 2014
Published: 5 November 2014
The electron beam melting (EBM) Ti-6Al-4V material technology has been developed over a short time period. It was introduced through a research to develop Ti-6Al-4V implants for patients, but EBM printed locking compression plates have not been used for clinical implants. The main purpose of this study is to find whether the EBM Ti-6Al-4V plate suit for clinical implants.
First, we scanned an AO-locking compression plate (LCP) and printed LCP samples using EBM. Next, we evaluated the EBM plate surface roughness through optical microscopy as well as the LCP and EBM plates’ mechanical characteristics using the ASTM standard, which is commonly used to test the mechanical properties of bone plates subject to bending. Each sample was examined using a single-cycle four-point bending test and hardness testing to acquire data on bending stiffness, bending strength, bending structural stiffness, and hardness.
The results show significant differences in bending stiffness, bending strength, bending structural stiffness, and hardness between the samples using EBM and the original LCP plates. The EBM-printed samples’ surface roughness was 0.49 ± 0.02 μm. The mean hardness of the LCP sample was 266.67 HV10 ± 5.8, and the EBM-printed sample mean hardness was 341.1 HV10 ± 1.93. The EBM samples' bending stiffness was 87.67%, which is greater than using the LCP plates'; and the bending strength was 190.7% greater, the bending structural stiffness was 73.2% greater, and the hardness was 27.9% greater.
The results show that the EBM plates' general mechanical strength was significantly greater than the LCP plates. An EBM plate is advantageous for clinical implants because it can be customized with great potential for improvement.
The locking compression plate (LCP) is part of the newest generation of AO plate fixation systems, and it yields good clinical efficacy and satisfaction according to clinical surveys -. The LCP stability depends on the angular interface between the screw and plate rather than the friction force between the plate and bone. Thus, the plate cannot contact the bone when it is implanted. On the other hand, due to the low pressure on the periosteum, the LCP has little influence on the bone blood supply. In general, LCP provides stable angulation fixation and relatively safe biological environment around the fracture area with little destruction to the periosteum or bone blood supply, which consequently, favors union with the bone , especially for patients with poor quality bones and delayed union or non-union .
Electron beam melting (EBM) is a form of 3D printing; 3D printing technology rapidly manufactures objects with various complex shapes based on a computer-aided design model or computed tomography data. Different forms of 3D printing technology and many additive processes are available. Their differences lie in the production of layered parts and materials, including selective laser melting (SLM), direct metal laser sintering (DMLS), selective laser sintering (SLS), and fused deposition modeling (FDM). Other researchers use different advanced technologies to cure the liquid material, such as stereo lithography (SLA) and laminated object manufacturing (LOM).
As a rapid manufacturing method, EBM is suitable for metal parts. The technology rapidly manufactures products with strong structures, especially implants and prostheses. Unlike traditional SLS, a high-power electron beam, rather than a laser beam, is used for EBM procedures. Because metal powder leads to light reflex during sintering, the production process is much faster. High-quality implants or prostheses are fully constructed using melted metal particles, which ensure that the products are completely void free. The full EBM process occurs in an ultra-high-vacuum environment, which prevents defects caused by oxidation. In conclusion, EBM is a reliable manufacturing technique.
Currently, the application fields for 3D printing have expanded. In orthopedic and maxillofacial surgery, implants are typically required to replace damaged or removed tissue to restore its function and appearance. However, current implants for clinical use are manufactured in a fixed pattern that does not perfectly match the patient's defect. Especially for maxillofacial surgery, it is more difficult to generate patient-specific implants or prostheses due to the extraordinary demand in maxillofacial surgery. However, these implants can be printed in accordance with CT, MRI, or other imaging data on each patient through 3D printing technology, such as LCP, which rapidly manufactures implants that are personalized.
Previous studies have shown that materials, such as Ti-6Al-4V, can be utilized to manufacture implants or prostheses ,. Cellular biomaterials fabricated using EBM have been widely used due to their good osteoinductive properties  and mechanical properties, as demonstrated in researches of bone tissue engineering studies. Relative tests have been conducted to measure their stiffness, and the results suggest that the mechanic behavior of the biomaterials in the cellular microstructure is similar to a cancellous bone ; thus, it is suitable for printing implants or prostheses using EBM for clinical applications. Harrysson et al. fabricated hip stems using Ti-6Al-4V ; Derand et al. also reported that a lower jawbone implant was printed through EBM . Implants or prostheses for such specific human bone part typically require highly individualized customization. Because an upper extremity internal fixation system requires relatively lower mechanical strength, we printed LCP superior anterior clavicle plates using EBM. Next, we proceeded to a mechanical test to find whether the EBM Ti-6Al-4V plate suit for clinical implants. Based on the results, we may have generated a new way to manufacture plates.
Materials and methods
EBM-printed LCP plates
Three LCP plates (3 holes, 3.5 mm LCP superior anterior clavicle plates with lateral extension) and their EBM counterparts were used for the mechanical tests. For each plate, a four-point bending test was performed using the axial torsional biomechanical testing system (Shore Western 301.6, USA); the load cell was Interface 1216CEW-2 K (Interface, USA).
The plate was positioned at the bone interface, and it contacted the roller shaft surface, which positioned the plate at the bone interface and forced it to contact the roller shaft surface. Displacement-controlled testing was used at 0.1 mm/sec until plastic deformation was reached; the displacement and load data from sensors were used to establish the bending stiffness of each bone plate as defined by the ASTM standard  for the maximum slope in the linear elastic portion of the load versus load-point displacement curve (N/mm). The preload was 100 N. The loads were applied through the rollers with equal diameters in the range 6 mm. Each plate was positioned medially. Two screw holes were positioned between the two loading rollers. The distance between the two support rollers was 54 mm; it was 26 mm between the loading rollers. The bending moment deflection curves were generated using Microsoft Excel, and the line that represents the slope for bending stiffness was offset by a 0.052-mm displacement; this line is superimposed on the chart. The point where the bending moment-deflection curves intersects the offset bending stiffness slope is the bending strength, which is reported in N ± m. The bending structural stiffness depends on bending rigidity, span center, and loading span. The computation formula used was the following: EI e = ((2 h +3a)Kh 2)/12, where `K’ is the bending stiffness, `a’ is the center span distance (26 mm), and `h’ is the loading span distance (14 mm) used to apply the controlled force and to collect the load and actuator position data.
Optical microscopy and surface roughness measurement
The hardness was examined to discern the local strength of the materials at specific points, whereas the data significance for the whole material was determined using statistical means. As the most widely used method for investigating mechanical properties, examining the hardness shows each material's differences in both chemistry and structural organization based on the manufacturing technique.
The hardness was investigated to evaluate the mechanical properties of the plates. The hardness was examined using Vicker's test method; we examined the macro-hardness. Due to the sample size, the tests were performed at three different locations for micro-hardness testing (DHV-1000; Shanghai Material Testing Machine; Shanghai Corp; Shanghai; China). The indentations were generated with a 10-kg load and the standard indentation time was 15 s; each sample was examined (3 LCP and 3 EBM samples; n =18).
The data are expressed as the mean ± standard deviation. Two-way analyses of variance (ANOVA) were performed to detect significant differences through ROM using SPSS software (version 17.0, SPSS, IBM Corp., Armonk, NY, USA). The significance used was P <0.05.
Summary of plate hardness, bending stiffness (N/mm), bending strength (N ± m), and bending structural stiffness (N ± m 2 )
Bending stiffness (N ± mm)
Bending strength (N/m)
Bending structural stiffness (N ± m2)
341.1 ± 1.93
716.32 ± 4.41
15.1 + 0.50
1.23 ± 0.01
266.67 ± 5.8
381.68 ± 6.52
5.194 ± 0.08
0.71 ± 0.05
The purpose of our study is to compare in vitro mechanical properties of EBM manufactured LCP samples with original LCP plates and to test their mechanical characteristics to determine whether the EBM plates meet the standard for clinical application. The samples' in vitro mechanical properties were examined using the ASTM standard.
The same curves were reported by DeTora et al. , but the maximum yield strength was not reported; his LCP data differ from ours. We think that the difference may result from the different loading conditions and LCP plate types.
Eden et al. compared a seven-hole superior anterior clavicle LCP with a seven- and ten-hole reconstruction plate . The clavicle LCP revealed an elastic bending stiffness with a linear slope until failure (three-point bending test). His curves were similar to ours; both the EBM (Figure 4b) and LCP (Figure 4a) plates showed a linear slope until failure in the load-to-failure test. The hardness experiment herein showed that the LCP hardness was 266.67 HV 10 ± 5.8. Peivandi et al. tested failed orthopedic implants from 23 patients; the hardness examinations showed that the implants were within the standard range 280-290 HV . His result is similar to ours.
The EBM plate mean hardness was 341.1 HV10 ± 1.93, which is greater than in traditional implants.
In addition to the high strength, EBM has the advantage of custom design. LCP plates are not the only implants that EMB can produce. For example, prostheses for maxillofacial surgery and stomatology can also be manufactured using EBM technology. Recently, lower jaw or tooth prostheses were produced with various sizes. The designs are not always suitable for certain patients, but only the common type may be available, which may affect treatment . Derand et al.  described a method for imaging via virtual design to manufacture patient-specific titanium reconstruction plates and its utility for surgically treating acquired bone defects in the mandible using additive manufacturing through EBM. For patients who require bone plates, especially elderly patients or children, EBM can provide suitable patient-specific plates.
The research of Toksvig-Larsen et al.  shows that the contact rate between implant and bone is only average 53%, thus easily lead to stress concentration, influence bone growth, even the bone connection looseness. So the current implants are needed for a certain degree of personalized correction, and doctors may spend a lot of time for a steel plate to meet patient skeletal shape. Personalized plate can solve this problem through the design and customization in advance. We have verified the strength of EBM printed LCP plates, it can be modified and optimized more reasonable for patients in premise to reasonable strength.
We observed the surface scratches and rough areas as well as evaluated the EBM samples' roughness. The EBM plate surface is rough with an irregular texture, and its average roughness value was Ra =0.49 ± 0.02 μm. The implants should be polished to prevent friction between the plate and surrounding soft tissue. We also did not find the screw thread. The post process must be completed to resolve these inadequacies due to EBM inaccuracy.
EBM is also useful for porous titanium processing. To reduce its elastic modulus, designing implants with porous titanium can provide a lower bend modulus to decrease stress shielding ,; implants with a porous titanium surface also facilitate bone ingrowth and are biocompatible ,,. Thus, we imagine that a porous plate surface can be designed to contact the bone, which will enhance the plate internal fixation system stability and reduce the friction between the plate and surrounding soft tissue. It may also effectively reduce the effects of stress shielding and promote bone union.
In conclusion, this study shows the mechanical superiority of EBM plates compared with the locking compression plate. The recommended testing configuration wherein the loading rollers are positioned at approximately one-third distance between the supporting rollers was not used due to the sample size. Therefore, our data and results cannot be compared with similar studies. However, we compared the EBM plates to the locking compression plate under the same conditions; the EBM plates' general mechanical strength was significantly greater than the LCP plates, and EBM plate is advantageous because it can be customized with great potential for improvements.
This work was supported by the Natural Science Foundation of Shanghai, China (grant no. 14ZR1432600). Peng-cheng Liu and Yun-ji Yang are co-first authors.
- Sommer C, Gautier E, Muller M, Helfet DL, Wagner M: First clinical results of the locking compression plate (LCP). Injury. 2003, 34 (Suppl 2): B43-B54. 10.1016/j.injury.2003.09.024.View ArticlePubMedGoogle Scholar
- Zeman J, Matejka J, Matejka T, Salasek M, Zeman P, Nepras P: Open reduction and plate fixation (ORIF LCP) for treatment of bilateral calcaneal fractures. Acta Chir Orthop Traumatol Cech. 2013, 80 (2): 142-147.PubMedGoogle Scholar
- Umer M, Abbas K, Khan S, Rashid HU: Locking compression plate in musculoskeletal oncology `a friend in need’. Clin Orthop Surg. 2013, 5 (4): 321-326. 10.4055/cios.2013.5.4.321.PubMed CentralView ArticlePubMedGoogle Scholar
- Kumar MN, Ravindranath VP, Ravishankar M: Outcome of locking compression plates in humeral shaft nonunions. Indian J Orthop. 2013, 47 (2): 150-155. 10.4103/0019-5413.108899.PubMed CentralView ArticlePubMedGoogle Scholar
- Khan SA, Shamshery P, Gupta V, Trikha V, Varshney MK, Kumar A: Locking compression plate in long standing clavicular nonunions with poor bone stock. J Trauma. 2008, 64 (2): 439-441. 10.1097/01.ta.0000238716.97303.b3.View ArticlePubMedGoogle Scholar
- Harrysson OLA, Cansizoglu O, Marcellin-Little DJ, Cormier DR, West HA: Direct metal fabrication of titanium implants with tailored materials and mechanical properties using electron beam melting technology. Mat Sci Eng C. 2008, 28 (3): 366-373. 10.1016/j.msec.2007.04.022.View ArticleGoogle Scholar
- Murr LE, Amato KN, Li SJ, Tian YX, Cheng XY, Gaytan SM, Martinez E, Shindo PW, Medina F, Wicker RB: Microstructure and mechanical properties of open-cellular biomaterials prototypes for total knee replacement implants fabricated by electron beam melting. J Mech Behav Biomed Mater. 2011, 4 (7): 1396-1411. 10.1016/j.jmbbm.2011.05.010.View ArticlePubMedGoogle Scholar
- Rapuano BE, Singh H, Boskey AL, Doty SB, MacDonald DE: Heat and radiofrequency plasma glow discharge pretreatment of a titanium alloy: evidence [corrected] for enhanced osteoinductive properties. J Cell Biochem. 2013, 114 (8): 1917-1927. 10.1002/jcb.24536.View ArticlePubMedGoogle Scholar
- Cheng XY, Li SJ, Murr LE, Zhang ZB, Hao YL, Yang R, Medina F, Wicker RB: Compression deformation behavior of Ti-6Al-4 V alloy with cellular structures fabricated by electron beam melting. J Mech Behav Biomed Mater. 2012, 16: 153-162. 10.1016/j.jmbbm.2012.10.005.View ArticlePubMedGoogle Scholar
- Derand P, Rannar LE, Hirsch JM: Imaging, virtual planning, design, and production of patient-specific implants and clinical validation in craniomaxillofacial surgery. Craniomaxillofac Trauma Reconstr. 2012, 5 (3): 137-144. 10.1055/s-0032-1313357.PubMed CentralView ArticlePubMedGoogle Scholar
- Specification and Test Method for Metallic Bone Plates. ASTM International; 2008.Google Scholar
- DeTora M, Kraus K: Mechanical testing of 3.5 mm locking and non-locking bone plates. VCOT. 2008, 21 (4): 318-322.PubMedGoogle Scholar
- Eden L, Doht S, Frey SP, Ziegler D, Stoyhe J, Fehske K, Blunk T, Meffert RH: Biomechanical comparison of the locking compression superior anterior clavicle plate with seven and ten hole reconstruction plates in midshaft clavicle fracture stabilisation. Int Orthop. 2012, 36 (12): 2537-2543. 10.1007/s00264-012-1671-x.PubMed CentralView ArticlePubMedGoogle Scholar
- Peivandi MT, Yusof-Sani MR, Amel-Farzad H: Exploring the reasons for orthopedic implant failure in traumatic fractures of the lower limb. Arch Iran Med. 2013, 16 (8): 478-482.PubMedGoogle Scholar
- Harrysson OLA, Cormier DR: Direct Fabrication of Custom Orthopedic Implants Using Electron Beam Melting Technology. 2005, John Wiley & Sons, LtdView ArticleGoogle Scholar
- Toksvig-Larsen S, Ryd L: Surface characteristics following tibial preparation during total knee arthroplasty. J Arthroplasty. 1994, 9 (1): 63-66. 10.1016/0883-5403(94)90138-4.View ArticlePubMedGoogle Scholar
- Parthasarathy J, Starly B, Raman S, Christensen A: Mechanical evaluation of porous titanium (Ti6Al4V) structures with electron beam melting (EBM). J Mech Behav Biomed Mater. 2010, 3 (3): 249-259. 10.1016/j.jmbbm.2009.10.006.View ArticlePubMedGoogle Scholar
- Bandyopadhyay A, Espana F, Balla VK, Bose S, Ohgami Y, Davies NM: Influence of porosity on mechanical properties and in vivo response of Ti6Al4V implants. Acta Biomater. 2010, 6 (4): 1640-1648. 10.1016/j.actbio.2009.11.011.PubMed CentralView ArticlePubMedGoogle Scholar
- Wu SH, Li Y, Zhang YQ, Li XK, Yuan CF, Hao YL, Zhang ZY, Guo Z: Porous titanium-6 aluminum-4 vanadium cage has better osseointegration and less micromotion than a poly-ether-ether-ketone cage in sheep vertebral fusion. Artif Organs. 2013, 37 (12): E191-E201. 10.1111/aor.12153.View ArticlePubMedGoogle Scholar
This article is published under license to BioMed Central Ltd. This is an Open Access article distributed under the terms of the Creative Commons Attribution License (http://creativecommons.org/licenses/by/4.0), which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly credited. The Creative Commons Public Domain Dedication waiver (http://creativecommons.org/publicdomain/zero/1.0/) applies to the data made available in this article, unless otherwise stated.