Preparation of interconnected highly porous polymeric structures by a replication and freeze‐drying process

Hou, Qingpu; Grijpma, Dirk W.; Feijén, Jan

doi:10.1002/jbm.b.10066

Cited by 114 publications

(74 citation statements)

References 35 publications

(30 reference statements)

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“…Evident differences between AS and GS surfaces of obtained polymer and composite membranes were found. AS surfaces of materials prepared by TIPS method exhibited open, irregular, cellular microporous structure, a typical morphology formed by solid-liquid phase separation [12][13][14]. Pore size decreased, and their shape become more regular upon addition of BG particles.…”

Section: Resultsmentioning

confidence: 99%

“…Phase separation methods, predominantly the nonsolvent-induced phase separation (NIPS, also called as immersion-precipitation) [3,10,11] and the thermalinduced phase separation (TIPS) [10,[12][13][14][15] techniques have been used to obtain porous polymer, as well as polymer-ceramic composite scaffolds and membranes for TE applications. The obtained material morphology, as well as the corresponding pore size and shape may vary widely depending on the manufacturing process conditions; from dense to highly porous, and with pores size from submicron scale to tens of microns.…”

Section: Introductionmentioning

confidence: 99%

“…TIPS is a versatile processing method allowing considerable control over membrane and scaffold microstructure. Adjusting the parameters of the TIPS process, such as polymer type, polymer concentration, quenching temperature and time, and the cooling rate, can lead to porous polymer and composite constructs with distinctive architectures, tailored to the target applications [14,15,17].…”

Section: Introductionmentioning

confidence: 99%

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Poly(ε-caprolactone)-based membranes with tunable physicochemical, bioactive and osteoinductive properties

Dziadek¹,

Zagrajczuk²,

Menaszek

et al. 2017

J Mater Sci

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In contrast to currently used materials, membranes for the treatment of bone defects should actively promote regeneration of bone tissue beyond their physical barrier function. What is more, both material properties and biological features of membranes should be easily adaptable to meet the needs of particular therapeutic applications. Therefore, the role of preparation methods (nonsolvent-induced phase separation and thermal-induced phase separation) of poly(ε-caprolactone)-based membranes and their modification with gel-derived bioactive glass (BG) particles of two different sizes (\45 and \3 μm) in modulating material morphology, polymer matrix crystallinity, surface wettability, kinetics of in vitro bioactivity and also osteoblast response was investigated. Both surfaces of membranes were characterised in terms of their properties. Our results indicated a possibility to modulate microstructure (pore size ranging from submicron to hundreds of micrometres), wettability (from hydrophobic to fully wettable surface) and polymer crystallinity (from 19 to 60%) in a wide range by the use of various preparation methods and different BG particle sizes. Obtained composite membranes showed excellent in vitro hydroxyapatite forming ability after incubation in simulated body fluid. Here we demonstrated that bioactive layer formation on the surface of membranes occurred through ACP-OCP-CDHA-HCA transformation, that mimic in vivo bone biomineralization process. Composite membranes supported human osteoblast proliferation, stimulated cell differentiation and matrix mineralization. We proved that kinetics of bioactivity process and also osteoinductive properties of membranes can be easily modulated with the use of proposed variables. This brings new

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Section: Resultsmentioning

confidence: 99%

Section: Introductionmentioning

confidence: 99%

Section: Introductionmentioning

confidence: 99%

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Poly(ε-caprolactone)-based membranes with tunable physicochemical, bioactive and osteoinductive properties

Dziadek¹,

Zagrajczuk²,

Menaszek

et al. 2017

J Mater Sci

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“…Previously, Hou et al [25] fabricated high porosity PDLLA foams and found the compressive moduli of scaffolds of 97.2% and 97.7% porosity to be 0.30 MPa and 0.23 MPa, respectively. In another study, Hou et al [26] related compressive moduli to the porosities of the scaffolds according to the power law relationship (Eq.…”

Section: Theoretical Modellingmentioning

confidence: 99%

Mechanical properties of highly porous PDLLA/Bioglass® composite foams as scaffolds for bone tissue engineering

et al. 2005

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This study developed highly porous degradable composites as potential scaffolds for bone tissue engineering. These scaffolds consisted of poly-D,L-lactic acid filled with 2 and 15 vol.% of 45S5 Bioglass® particles and were produced via thermally induced solid-liquid phase separation and subsequent solvent sublimation. The scaffolds had a bimodal and anisotropic pore structure, with tubular macro-pores of ~100 µm in diameter, and with interconnected micro-pores of ~10-50 µm in diameter. Quasi-static and thermal dynamic mechanical analysis carried out in compression along with thermogravimetric analysis was used to investigate the effect of Bioglass® on the properties of the foams. Quasi-static compression testing demonstrated mechanical anisotropy concomitant with the direction of the macro-pores. An analytical modelling approach was applied, which demonstrated that the presence of Bioglass® did not significantly alter the porous architecture of these foams and reflected the mechanical anisotropy which was congruent with the scanning electron microscopy investigation. This study found that the Ishai-Cohen and Gibson-Ashby models can be combined to predict the compressive modulus of the composite foams. The modulus and density of these complex foams are related by a power-law function with an exponent between 2 and 3.

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“…Different porogens are used frequently for the leaching techniques. These are, for example, NaCl [258], as perhaps the most common leaching substance, as well as paraffin spheres [170,259,260], sugar crystals [261][262][263] or gelatin [264], which serve as place holders for pores and their interconnections in the actual scaffold formation process. These spacers are removed by leaching following the main processing step.…”

Section: Leaching Techniquementioning

confidence: 99%

Design and preparation of polymeric scaffolds for tissue engineering

Weigel

Schinkel

Lendlein

2006

Expert Review of Medical Devices

208

154

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Polymeric scaffolds for tissue engineering can be prepared with a multitude of different techniques. Many diverse approaches have recently been under development. The adaptation of conventional preparation methods, such as electrospinning, induced phase separation of polymer solutions or porogen leaching, which were developed originally for other research areas, are described. In addition, the utilization of novel fabrication techniques, such as rapid prototyping or solid free-form procedures, with their many different methods to generate or to embody scaffold structures or the usage of selfassembly systems that mimic the properties of the extracellular matrix are also described. These methods are reviewed and evaluated with specific regard to their utility in the area of tissue engineering.Expert Rev. Med. Devices 3(6), 835-851 (2006) The technology of tissue engineering aims to generate new or substitute damaged or malfunctioning tissue or organs and could well become an alternative method to whole organ transplantation [1][2][3][4][5][6]. In the last decade particularly, enormous advances have been made in the area of tissue regeneration for therapeutical purposes. Tissue engineering is an interdisciplinary research area in which principles of material science/engineering and cell biology/life science are combined. The methods of tissue engineering have been applied to different types of tissue, including skin [7][8][9][10][11], bone [12][13][14][15][16], liver [17][18][19][20][21], intestine [22][23][24][25][26][27], esophagus [28][29][30][31][32], valve leaflets [33][34][35][36], muscle [37][38][39] and tongue [40][41][42], the vascular system [43][44][45][46][47], for craniofacial defects [48][49][50], tendons and ligaments [51][52][53][54][55], cartilage [56][57][58][59][60] and nerve tissue [61][62][63][64][65]. Since the early commercialization of tissue-engineered applications, for example, the work of Bell and colleagues [66], research with stem cells [3,[67][68][69] and the use of growth factors [70][71][72][73] that support cell differentiation and proliferation, have provided new opportunities in the field of tissue engineering. At present, tissue engineering methods generally require the use of a porous scaffold that serves as a matrix for initial cell attachment and subsequently for tissue formation in vitro and in vivo. Up to now scaffolds made from biomaterials have temporarily substituted the extracellular matrix (ECM). Such biomaterials can be of natural origin, such as organic collagen [74][75][76], fibrin glue [77][78][79], hyaluronic acid [80][81][82] or the inorganic-like coralline [83,84]. Synthetic polymeric materials have also been investigated, including, for example, aliphatic, copolyesters [85][86][87], polyhydroxyalkanoates [88][89][90] and polyethylene glycol [91,92], or inorganic materials, such as hydroxyapatite [48,93,94], tricalciumphosphate [95,96], glass ceramics and glass [97][98][99].The intrinsic material properties, such as the mechanical [100] or thermal [101,102] be...

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Preparation of interconnected highly porous polymeric structures by a replication and freeze‐drying process

Cited by 114 publications

References 35 publications

Poly(ε-caprolactone)-based membranes with tunable physicochemical, bioactive and osteoinductive properties

Poly(ε-caprolactone)-based membranes with tunable physicochemical, bioactive and osteoinductive properties

Mechanical properties of highly porous PDLLA/Bioglass® composite foams as scaffolds for bone tissue engineering

Design and preparation of polymeric scaffolds for tissue engineering

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