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Logo of nihpaAbout Author manuscriptsSubmit a manuscriptNIH Public Access; Author Manuscript; Accepted for publication in peer reviewed journal;
 
Int J Polym Sci. Author manuscript; available in PMC Oct 25, 2011.
Published in final edited form as:
Int J Polym Sci. 2010; 2010: 270273.
doi:  10.1155/2010/270273
PMCID: PMC3201805
NIHMSID: NIHMS222243
Effects of composite formulation on the mechanical properties of biodegradable poly(propylene fumarate)/bone fiber scaffolds
Xun Zhu, Nathan Liu, Michael J. Yaszemski, and Lichun Lu*
Departments of Orthopedic Surgery and Biomedical Engineering, Mayo Clinic College of Medicine, 200 First Street SW, Rochester, MN 55905
*Corresponding author: Lichun Lu, Ph.D., Associate Professor, Departments of Orthopedic Surgery and Biomedical Engineering, Mayo Clinic College of Medicine, 200 1st Street SW, MS 3-69, Rochester, MN 55905, Tel: (507) 284-2667, Fax: (507) 284-5075, lu.lichun/at/mayo.edu
The objective of our study was to determine the effects of composite formulation on the compressive modulus and ultimate strength of a biodegradable, in situ polymerizable poly(propylene fumarate) (PPF) and bone fiber scaffold. The following parameters were investigated: the incorporation of bone fibers (either mineralized or demineralized), PPF molecular weight, N-vinyl pyrrolidinone (NVP) crosslinker amount, benzoyl peroxide (BP) initiator amount, and sodium chloride porogen amount. Eight formulations were chosen based on a resolution III two level fractional factorial design. The compressive modulus and ultimate strength of these formulations were measured on a materials testing machine. Absolute values for compressive modulus varied from 21.3 to 271 MPa and 2.8 to 358 MPa for dry and wet samples, respectively. The ultimate strength of the crosslinked composites varied from 2.1 to 20.3 MPa for dry samples and from 0.4 to 16.6 MPa for wet samples. Main effects of each parameter on the measured property were calculated. The incorporation of mineralized bone fibers and an increase in PPF molecular weight resulted in higher compressive modulus and ultimate strength. Both mechanical properties also increased as the amount of benzoyl peroxide increased or the NVP amount decreased in the formulation. Sodium chloride had a dominating effect on the increase of mechanical properties in dry samples but showed little effects in wet samples. Demineralization of bone fibers led to a decrease in the compressive modulus and ultimate strength. Our results suggest that bone fibers are appropriate as structural enforcement components in PPF scaffolds. The desired orthopaedic PPF scaffold might be obtained by changing a variety of composite formulation parameters.
Keywords: poly(propylene fumarate), bone fiber, orthopaedic biomaterials, injectable, mechanical properties
There has been a great need for the treatment of skeletal defects which may result from tumors, trauma, or abnormal development [1]. The current methods for restoring tissue structure and function rely mostly on autograft and allograft [24]. Both methods, while appropriate for management of many bone defects, do have certain limitations. These include donor site morbidity after autograft harvesting and slow incorporation of cortical allograft. The other materials commonly used such as polymers, ceramics, and metals all have their associated drawbacks, such as poor integration with the host tissue, stress-shielding of adjacent bone, and osteolysis from particulate wear debris [5]. The treatment regimen could be improved with the availability of a skeletal regeneration biomaterial that could be processed into the specific shape needed, provide structural support required, be replaced by new, vascularized bone tissue, and then disappear to allow the new bone to remodel along local stress lines.
Poly(propylene fumarate) (PPF) is an unsaturated linear polyester with fumarate double bonds that can be crosslinked in situ. It is biocompatible, biodegradable, osteoconductive, and capable of both pre-formed and injectable applications [69]. PPF scaffolds can be used to fill irregularly shaped defects with minimal surgical intervention. They possess mechanical properties on the order of magnitude of human trabecular bone. The fabrication of biodegradable polymer composites based on PPF for orthopaedic applications has been the subject of investigation in our laboratory [10, 1112]. The properties of the produced composites can be tailored for specific applications by varying different parameters including crosslinking density and fillers [1011, 1314]. The composite formulation can include a porogen such as NaCl for initial porosity and a particulate ceramic such as β-tricalcium phosphate (TCP) for mechanical reinforcement and increased osteoconductivity.
Mineralized bone fibers (MBF) are obtained by processing allograft bone. The technique involves shaving the cortical bone to produce bone fibers. MBFs have a composition identical to bone and may be used for structural reinforcement of scaffolds. They have been shown to increase the initial compressive strength of PPF/PPF-DA scaffolds [11]. The acidification of MBF produces demineralized bone fibers (DBF), which consist of non-mineral components of MBF and have accessible bone inductive factors. Demineralized bone matrices (DBM) have extremely high osteoinductive properties and greatly improve the integration of autogenous bone grafts in the skull [15]. In the various forms of DBM, the fiber-based grafts produced the largest new bone in a critical size cranial defect in athymic rats [16]. These grafts were found to perform as well as autografts [16]. Therefore, the incorporation of bone fibers in PPF scaffolds not only provides a structural support component but could also promote bone regeneration in bone defects.
In this study, experiments were designed to study the effects of various processing parameters, such as PPF molecular weight, incorporation of bone fibers (MBF or DBF), crosslinker amount, initiator amount, and porogen amount, on the ultimate strength and compressive modulus of PPF/bone fiber scaffolds.
2.1. Raw materials
Fumaryl chloride (Aldrich, Milwaukee, WI) was purified by distillation under nitrogen atmosphere. Demineralized bone fibers (DBF) were obtained through acidification wash of mineralized bovine bone fibers (MBF) (OsteoTech Inc.). Propylene glycol, N-vinyl pyrrolidinone (NVP), N,N-dimenthyl-p-toluidene (DMT), benzoyl peroxide (BP) and sodium chloride were purchased from Aldrich Chemical (Milwaukee, WI) and used as received. All solvents were purchased from Fisher (Pittsburgh, PA) as reagent grade and used as received. Sodium chloride was sieved to obtain particles in a 106–300 µm size range and used as porogen. All experiments described below were based on a Resolution III two-level fractional factorial design varying six parameters. The six parameters included PPF molecular weight, NVP to PPF ratio, BF to polymer (PPF/NVP) ratio, BF type, BP to PPF ratio, and the percentage of NaCl in the composites. The experimental design and the values for all parameters are presented in Table I.
2.2. PPF Synthesis
PPF was synthesized by a two-step reaction process as described previously [17]. Briefly, fumaryl chloride was added dropwise to a solution of propylene glycol in methylene chloride at 0°C under nitrogen in the presence of K2CO3. After addition of fumaryl chloride, the reaction mixture was stirred for an additional 2 h at 0°C before water was added to dissolve the inorganic salt. The organic phase was separated and dried over Na2SO4. After filtration of the mixture and evaporation of the solvent, the formed di(2-hydroxylpropyl) fumarate was converted to PPF by transesterification at 160°C and 0.5 mmHg. The produced polymer was purified by solution precipitation forming a viscous liquid. Gel permeation chromatography with a differential refractometer (Waters 410, Milford, MA) was used to determine polymer molecular weight distributions. A Phenogel column (300 × 7.8 mm, 5 nm, mixed bed, Phenomenex, Torrance, CA) and a Phenogel guard column (7.8 mm, 5 nm, mixed bed, Phenomenex) were employed for the elution of polymer solution in chloroform at flow rate of 1 ml/min. Polystyrene standards were utilized to obtain a calibration curve for calculating the polymer molecular weights.
2.3. Demineralization of bone fibers
MBF were weighed to the nearest gram and soaked in 15 volume of a 0.6 N HCl solution with 0.025% Triton X-100. When the pH of the solution was more than 1, the acid was decanted and replaced with another 15 volume of fresh 0.6 N HCl without triton. PH readings were taken every ten minutes until it is more than 1. The acid was carefully decanted and the same volume of distilled, deionized water (ddH2O) was added. The water wash was repeated several times until the pH is greater than 3. The resulting DMF were soaked in 70% ethanol for 30 min. and collected on a 106 µm sieve. DMF were washed again with ddH2O and freeze-dried for 24 hrs.
2.4. Experimental design
All experiments described below were based on a Resolution III two-level fractional factorial design varying six parameters [18]. The experimental design and the values for all parameters are presented in Table I. Six processing parameters were varied to determine their effects on mechanical properties of the composite scaffolds. The high (+) and low (−) values for all parameters are listed (Table IA). The number average molecular weights (Mn) of PPF were chosen as 4000 and 2000. The ratios of NVP to PPF were 0.7 and 0.5 ml per gram. The weight percentages of bone fibers to polymer were 20% and 0%. The weight percentages of BP were 0.5% and 0.1%. The weight percentages of NaCl were 30% and 0%. The two levels for the factor called bone fiber type are DMF and MBF. High and low levels were then combined according to the resolution III design to create eight formulations (Table IB). This factorial design will demonstrates the effect that each parameter exhibits while minimizing the numbers of trials. The results from each experiment were examined to determine the main effects of each parameter on the measured property [18].
2.5. Scaffold preparation
The designated amount of monomer (NVP) was divided into two portions. Three-fourths of the monomer was combined with the PPF. The initiator (BP) was dissolved in the remaining one-fourth of the monomer and added to the polymer solution. The solid phase components (BF, NaCl) were added, followed by DMT. The resulting paste was immediately placed in 8-mm diameter glass vials. The resulting PPF cylinders (dry samples) were removed from the vials after overnight crosslinking. Half of the samples were incubated with phosphate buffered saline (PBS) for one day to leach out some of sodium chloride (wet samples). The scaffolds tested in this study had a diameter of 6 mm and a height of 20 mm.
2.6. Mechanical testing
Mechanical properties of both dry and wet samples were analyzed using a servohydraulic testing machine (MTS, Minneapolis, MN), as shown in Figure 1A. Sample length and diameter were measured before testing (Figure 1B). The specimens were placed between two solid platens and compressed at a rate of 0.1 mm/second (Figure 1C). Load and displacement were recorded using a digital computer (Figure 2). The stress-strain curve was plotted by determining stress as the load divided by the cross-sectional area and strain as the displacement divided by the initial length of the cylinder. Compressive modulus was calculated as the slope of the initial linear portion of the stress-strain curve, beginning at 1.0% strain. The highest strength achieved was the ultimate strength.
Figure 1
Figure 1
(A) The servohydraulic materials testing machine used in this study. (B) A representative PPF composite scaffold incorporating mineralized bone fibers and sodium chloride porogen. The PPF cylinder was approximately 6 mm in diameter and 20 mm in height. (more ...)
Figure 2
Figure 2
Load and displacement of the representative sample shown in Figure 1 were recorded during compression. The stress-strain curve was then plotted and compressive modulus was calculated as the slope of the initial linear portion of the stress-strain curve, (more ...)
2.7. Statistical analysis
All data are reported as means ± standard deviations (SD) for n = 4, except for size distribution measurements where SD was calculated based on normal distribution. Single factor analysis of variance (ANOVA) was used to assess the statistical significance of results. Scheffé’s method was employed for multiple comparison tests at significance levels of 95 and 99%.
This study was designed to determine the effects of six parameters on the ultimate stress and compressive modulus of PPF/bone fiber composite scaffolds. The six parameters included PPF molecular weight, NVP to PPF ratio, BF to polymer (PPF/NVP) ratio, BF type, BP to PPF ratio, and the percentage of NaCl in the composites. The ultimate stress and compressive modulus of all formulations were measured and values are given in Table II.
TABLE II
TABLE II
Summary of Results for Ultimate Strength and Compressive Modulus
3.1. Compressive modulus
Absolute values of compressive moduli varied from 21.3 to 271 MPa and 2.8 to 358 MPa for dry and wet samples, respectively (Table II). The results from each formulation were calculated to determine the effects of each parameter on the measured property (Figure 3). In dry samples, the presence of NaCl significantly increased the observed modulus values and overshadowed the effects contributed by other factors. This increased modulus was not seen in the corresponding wet samples. Therefore, the mechanical data from wet samples are more suitable for analysis of other effects. The incorporation of mineralized bone fibers and the increase of PPF molecular weight significantly increased the compressive modulus of PPF/NVP scaffolds. A decrease in monomer (NVP) led to an increase in compressive modulus. An increase in radical initiator (BP) was also found to increase the compressive modulus. Demineralization of bone fibers significantly decreased the compressive modulus of the scaffolds.
Figure 3
Figure 3
The main effects of the parameters on the compressive modulus of the crosslinked PPF composites. A positive number indicates an increase in the modulus as the parameter was changed from a low (−) level to a high (+) level. A negative number indicates (more ...)
3.2. Ultimate strength
The ultimate strength of the crosslinked composites varied from 2.1 to 20.3 MPa for dry samples and from 0.4 to 16.6 MPa for wet samples (Table II). Very similar to compressive modulus, the presence of NaCl in dry samples significantly increased the observed modulus values and overshadowed the effects contributed by other factors (Figure 4), a phenomena not observed in the corresponding wet samples. The incorporation of MBF and the increase of PPF molecular weight were found to increase the ultimate strength of PPF/NVP scaffolds dramatically. Ultimate strength also increased as the amount of benzoyl peroxide increased or the amount of NVP decreased in the composites. Demineralization of bone fibers significantly decreased the ultimate strength of the scaffolds.
Figure 4
Figure 4
The main effects of the parameters on the ultimate strength of the crosslinked PPF composites. A positive number indicates an increase in the strength as the parameter was changed from a low (−) level to a high (+) level. A negative number indicates (more ...)
Biodegradable PPF is a promising orthopedic material that may be used as injectable or preformed scaffolds to repair and regenerate bone defects [1921]. The components used to form PPF scaffolds have a large influence on its mechanical properties. The objective of our study was to measure the compressive modulus and ultimate strength to determine the effects of the incorporation of bone fibers, PPF molecular weight, NVP amount, BP amount, NaCl amount, and demineralization of bone fibers on these measured properties. It was the first time that the effects of the incorporation of bone fibers and demineralization of bone fibers on PPF scaffolds were investigated.
New and important factors have been identified to affect the mechanical properties of PPF/NVP scaffolds. The incorporation of mineralized bone fibers and an increase in PPF molecular weight resulted in higher compressive modulus and ultimate strength. Both mechanical properties also increased when the amount of benzoyl peroxide increased or the amount of NVP decreased. Sodium chloride had a dominating effect on the increase of mechanical properties in dry samples but showed little effects in wet samples. Demineralized bone fibers led to a decrease in the compressive modulus and ultimate strength.
Our results are consistent with a previous finding that compressive modulus and ultimate strength increased with increasing the amount of benzoyl peroxide and a decrease in NVP amount [13]. We also suggest that PPF molecular weight had great influence on the mechanical properties. At higher molecular weights (2000 to 5000), it was reported that PPF molecular weight did not affect the mechanical strength [13]. This result, however, was based on dry samples incorporating NaCl to determine the main effects. As shown in our study, the dominating effect of NaCl in dry samples masked the effects of other factors. Therefore, wet samples are more appropriate to determine the effects of factors other than NaCl.
We demonstrated for the first time that the incorporation of mineralized bone fibers in PPF/NVP scaffolds increases the mechanical properties significantly and in contrast, the incorporation of demineralized bone fibers decrease the mechanical properties significantly. Considering the fact that both bone fibers are biodegradable and DMF are osteoinductive, our results showed that PPF/bone fiber composites with a wide range of mechanical properties could be fabricated for different clinical uses.
In summary, we have identified the important factors that affect the compressive modulus and ultimate strength of PPF/bone fiber scaffolds. The desired orthopedic PPF scaffold might be obtained by varying these factors. Our results suggest that bone fibers are appropriate as structural enforcement components in PPF scaffolds, and may modulate other aspects of the synthetic biomaterials such as osteoconductivity.
Acknowledgements
This work was support by the John Smith Foundation, Mayo Foundation, and National Institutes of Health (R01 EB30005 and AR 45871).
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