Fabrication and evaluation of porous 2,3‐dialdehydecellulose membrane as a potential biodegradable tissue‐engineering scaffold

RoyChowdhury, P.; Kumar, Vijay

doi:10.1002/jbm.a.30503

Cited by 37 publications

(33 citation statements)

References 33 publications

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“…Oxidized cellulose is also promising as a carrier for controlled drug delivery (Zhu et al 2001). Oxidized dialdehyde cellulose has been applied as a biodegradable scaffold for tissue engineering (Roychowdhury and Kumar 2006), e.g. of vocal fold lamina propria (Roychowdhury et al 2009).…”

Section: Introductionmentioning

confidence: 99%

Cellulose-based materials as scaffolds for tissue engineering

et al. 2013

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Two types of cellulose-based materials, 6-carboxycellulose with 2.1 or 6.6 wt% of -COOH groups, were prepared and tested for potential use in tissue engineering. The materials were functionalized with arginine, i.e. an amino acid with a basic side chain, or with chitosan, in order to balance the relatively acid character of oxidized cellulose molecules, and were seeded with vascular smooth muscle cells (VSMC). The cell adhesion and growth were then evaluated directly on the materials, and also on the underlying polystyrene culture dishes. Of these two types of studied materials, 6-carboxycellulose with 2.1 wt% of -COOH groups was more appropriate for cell colonization. The cells on this material achieved an elongated shape, while they were spherical in shape on the other materials. The number of cells and the concentration (per mg of protein) of contractile proteins alpha-actin and SM1 and SM2 myosins, i.e. markers of the phenotypic maturation of VSMC, were also significantly higher on this material. Functionalization of the material with arginine and chitosan further improved the phenotypic maturation of VSMC. Chitosan also improved the adhesion and growth of these cells. In comparison with the control polystyrene dishes, the proliferation of cells on our cellulose-based materials was relatively low. This suggests that these materials can be used in applications where high proliferation activity of cells is not desirable, e.g. proliferation of VSMC on vascular prostheses. Alternatively, the cell proliferation might be enhanced by another more efficient modification, which would require further research.

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Section: Introductionmentioning

confidence: 99%

Cellulose-based materials as scaffolds for tissue engineering

et al. 2013

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“…However, applications in tissue engineering often require pore sizes in the upper micrometer range, for example, for skin (20-150 µm) or bone scaffolds (40-400 µm) [124], which cannot be realized with this technique unless it is combined with other processes, such as salt leaching [125]. Special shaped bodies prepared by 'pure' nonsolvent-induced phase separation (NIPS) can also be used in biomedical applications [126], for example, as a carrier for epidermal substitutes (FIGURE 1) [127].…”

Section: Scaffold Preparation From Polymer Solution By Nonsolvent-indmentioning

confidence: 99%

“…Thus, the objective of the leaching procedure is usually the realization of bigger pore sizes and increased interconnectivity. The use of the leaching technique in combination with injection [265] or compression molding [210,266], in combination with a NIPS [125], in gas foaming processes [150], as addendum of indirect SFF fabrication techniques [267], in combination with soft lithographic methods [268], photopolymerization [269] or in combination of coagulation with thermal processing [176], documents the comprehensive character of this technique.…”

Section: Leaching Techniquementioning

confidence: 99%

Design and preparation of polymeric scaffolds for tissue engineering

Weigel

Schinkel

Lendlein

2006

Expert Review of Medical Devices

210

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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“…Periodate oxidation has been performed on several types of cellulose including cotton linters (RoyChowdhury and Kumar 2006), microcrystalline cellulose (Kim et al 2004), cellulose powder derived from cotton and beech wood pulp (Maekawa and Koshijima 1984), and crystalline cellulose isolated from Cladophora sp. algae (Kim et al 2000).…”

Section: Introductionmentioning

confidence: 99%

“…There is evidence that DAC hydrolyzes at pH 7.4 into glycolic acid and 2,4-dihydroxybutyric acid. These are natural metabolic products found in mammalian systems and can be safely excreted from the body (Laurence et al 2005;Singh et al 1982;RoyChowdhury and Kumar 2006).…”

Section: Introductionmentioning

confidence: 99%

A resorbable calcium-deficient hydroxyapatite hydrogel composite for osseous regeneration

et al. 2009

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It was previously discovered that the unique structure and chemistry of bacterial cellulose (BC) permits the formation of calcium-deficient hydroxyapatite (CdHAP) nanocrystallites under aqueous conditions at ambient pH and temperature.In this study, BC was chemically modified via a limited periodate oxidation reaction to render the composite degradable and thus more suitable for bone regeneration. While native BC does not degrade in mammalian systems, periodate oxidation yields dialdehyde cellulose which breaks down at physiological pH. The composite was characterized by tensile testing, X-ray diffraction, Fourier transform infrared spectroscopy, and scanning electron microscopy. X-ray diffraction showed that oxidized BC retains its structure and could biomimetically form CdHAP. Degradation behavior was analyzed by incubating the samples in simulated physiological fluid (pH 7.4) at 37°C under static and dynamic conditions. The oxidized BC and oxidized BCCdHAP composites both lost significant mass after exposure to the simulated physiological environment. Examination of the incubation solutions by UV-Vis spectrophotometric analysis demonstrated that, while native BC released only small amounts of soluble cellulose fragments, oxidized cellulose releases carbonyl containing degradation products as well as soluble cellulose fragments. By entrapping CdHAP in a degradable hydrogel carrier, this composite should elicit bone regeneration then resorb over time to be replaced by new osseous tissue.

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Fabrication and evaluation of porous 2,3‐dialdehydecellulose membrane as a potential biodegradable tissue‐engineering scaffold

Cited by 37 publications

References 33 publications

Cellulose-based materials as scaffolds for tissue engineering

Cellulose-based materials as scaffolds for tissue engineering

Design and preparation of polymeric scaffolds for tissue engineering

A resorbable calcium-deficient hydroxyapatite hydrogel composite for osseous regeneration

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