Role of material surfaces in regulating bone and cartilage cell response

Boyan, Barbara D.; Hummert, Thomas W.; Dean, David D.; Schwartz, Zvi

doi:10.1016/0142-9612(96)85758-9

Cited by 1,212 publications

(737 citation statements)

References 70 publications

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“…Synthetic biodegradable polymers such as PCL, unlike natural ECM components, do not have specific cell-binding sides. Thus cell adhesion to pure synthetic polymers is poor and requires additional modifications such as adsorbing ECM proteins onto the polymer surface [48][49][50][51]. In our experiments, no additional surface modifications were necessary facilitating cell attachment onto the fibers of the hybrid scaffolds and both electrospun collagen/elastin/PCL and gelatin/PCL supported attachment and proliferation of hASCs.…”

Section: Discussionmentioning

confidence: 69%

Three-dimensional electrospun ECM-based hybrid scaffolds for cardiovascular tissue engineering

et al. 2008

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Electrospinning using natural proteins or synthetic polymers is a promising technique for the fabrication of fibrous scaffolds for various tissue engineering applications. However, one limitation of scaffolds electrospun from natural proteins is the need to cross-link with glutaraldehyde for stability, which has been postulated to lead to many complications in vivo including graft failure. In this study, we determined the characteristics of hybrid scaffolds composed of natural proteins including collagen and elastin, as well as gelatin, and the synthetic polymer poly(ε-caprolactone) (PCL), so to avoid chemical cross-linking. Fiber size increased proportionally with increasing protein and polymer concentrations, whereas pore size decreased. Electrospun gelatin/PCL scaffolds showed a higher tensile strength when compared to collagen/elastin/PCL constructs. To determine the effects of pore size on cell attachment and migration, both hybrid scaffolds were seeded with adipose-derived stem cells. Scanning electron microscopy and nuclei staining of cell-seeded scaffolds demonstrated complete cell attachment to the surfaces of both hybrid scaffolds, although cell migration into the scaffold was predominantly seen in the gelatin/PCL hybrid. The combination of natural proteins and synthetic polymers to create electrospun fibrous structures resulted in scaffolds with favorable mechanical and biological properties.

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Section: Discussionmentioning

confidence: 69%

Three-dimensional electrospun ECM-based hybrid scaffolds for cardiovascular tissue engineering

et al. 2008

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“…Reports investigating optimum pore sizes for various tissues generally recommend a pore size of 200 to 500 lm for bone [3,45]. Smaller pores may prevent cell infiltration or lead to insufficient vascularization and nutrient transport in vivo [24,35].…”

Section: Discussionmentioning

confidence: 99%

Do Surface Porosity and Pore Size Influence Mechanical Properties and Cellular Response to PEEK?

Torstrick

Evans

Stevens

et al. 2016

Clinical Orthopaedics &Amp; Related Research

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Background Despite its widespread use in orthopaedic implants such as soft tissue fasteners and spinal intervertebral implants, polyetheretherketone (PEEK) often suffers from poor osseointegration. Introducing porosity can overcome this limitation by encouraging bone ingrowth; however, the corresponding decrease in implant strength can potentially reduce the implant's ability to bear physiologic loads. We have previously shown, using a single pore size, that limiting porosity to the surface of PEEK implants preserves strength while supporting in vivo osseointegration. However, additional work is needed to investigate the effect of pore size on both the mechanical properties and cellular response to PEEK. Questions/purposes (1) Can surface porous PEEK (PEEK-SP) microstructure be reliably controlled? (2) What is the effect of pore size on the mechanical properties of PEEK-SP? (3) Do surface porosity and pore size influence the cellular response to PEEK? Methods PEEK-SP was created by extruding PEEK through NaCl crystals of three controlled ranges: 200 to 312, 312 to 425, and 425 to 508 lm. Micro-CT was used to characterize the microstructure of PEEK-SP. Tensile, fatigue, and interfacial shear tests were performed to compare the mechanical properties of PEEK-SP with injectionmolded PEEK (PEEK-IM). The cellular response to PEEK-SP, assessed by proliferation, alkaline phosphatase activity, vascular endothelial growth factor production, and calcium content of osteoblast, mesenchymal stem cell, and preosteoblast (MC3T3-E1) cultures, was compared with that of machined smooth PEEK and Ti6Al4V. Results Micro-CT analysis showed that PEEK-SP layers possessed pores that were 284 ± 35 lm, 341 ± 49 lm, and 416 ± 54 lm for each pore size group. Porosity and

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“…A literature review indicates that a pore size in the range of 10-400 lm may provide enough nutrient and osteoblast cellular infusion, while maintaining structural integrity. [185][186][187][188][189][190] A wide variety of fabrication techniques have been investigated to recreate the microscale porosity and special organization of native bone. Some examples of well developed techniques include: micromachining, photolithography, calcium-phosphate sintering, rapid prototyping, melt extrusion, salt leaching, emulsion templating, phase separation, fiber bonding, membrane lamination, and polymer demixing.…”

Section: Physical Effectors In Synthetic Bone Scaffoldsmentioning

confidence: 99%

Bone tissue engineering: A review in bone biomimetics and drug delivery strategies

Porter

Ruckh

Popat

2009

Biotechnology Progress

672

499

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Critical‐sized defects in bone, whether induced by primary tumor resection, trauma, or selective surgery have in many cases presented insurmountable challenges to the current gold standard treatment for bone repair. The primary purpose of a tissue‐engineered scaffold is to use engineering principles to incite and promote the natural healing process of bone which does not occur in critical‐sized defects. A synthetic bone scaffold must be biocompatible, biodegradable to allow native tissue integration, and mimic the multidimensional hierarchical structure of native bone. In addition to being physically and chemically biomimetic, an ideal scaffold is capable of eluting bioactive molecules (e.g., BMPs, TGF‐βs, etc., to accelerate extracellular matrix production and tissue integration) or drugs (e.g., antibiotics, cisplatin, etc., to prevent undesired biological response such as sepsis or cancer recurrence) in a temporally and spatially controlled manner. Various biomaterials including ceramics, metals, polymers, and composites have been investigated for their potential as bone scaffold materials. However, due to their tunable physiochemical properties, biocompatibility, and controllable biodegradability, polymers have emerged as the principal material in bone tissue engineering. This article briefly reviews the physiological and anatomical characteristics of native bone, describes key technologies in mimicking the physical and chemical environment of bone using synthetic materials, and provides an overview of local drug delivery as it pertains to bone tissue engineering is included. © 2009 American Institute of Chemical Engineers Biotechnol. Prog., 2009

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Role of material surfaces in regulating bone and cartilage cell response

Cited by 1,212 publications

References 70 publications

Three-dimensional electrospun ECM-based hybrid scaffolds for cardiovascular tissue engineering

Three-dimensional electrospun ECM-based hybrid scaffolds for cardiovascular tissue engineering

Do Surface Porosity and Pore Size Influence Mechanical Properties and Cellular Response to PEEK?

Bone tissue engineering: A review in bone biomimetics and drug delivery strategies

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