|Modifying three-dimensional scaffolds from novel nanocomposite materials using dissolvable porogen particles for use in liver tissue engineering.|
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|PMID: 22532408 Owner: NLM Status: MEDLINE|
|BACKGROUND: Although hepatocytes have a remarkable regenerative power, the rapidity of acute liver failure makes liver transplantation the only definitive treatment. Attempts to incorporate engineered three-dimensional liver tissue in bioartificial liver devices or in implantable tissue constructs, to treat or bridge patients to self-recovery, were met with many challenges, amongst which is to find suitable polymeric matrices. We studied the feasibility of utilising nanocomposite polymers in three-dimensional scaffolds for hepatocytes.
MATERIALS AND METHODS: Hepatocytes (HepG2) were seeded on a flat sheet and in three-dimensional scaffolds made of a nanocomposite polymer (Polyhedral Oligomeric Silsesquioxane [POSS]-modified polycaprolactone urea urethane) alone as well as with porogen particles, i.e. glucose, sodium bicarbonate and sodium chloride. The scaffold architecture, cell attachment and morphology were studied with scanning electron microscopy, and we assessed cell viability and functionality.
RESULTS: Cell attachment to the scaffolds was demonstrated. The scaffold made with glucose particles as porogen showed a narrower range of pore size with higher porosity and better inter-pore communications and seemed to encourage near normal cell morphology. There was a steady increase of albumin secretion throughout the experiment while the control (monolayer cell culture) showed a steep decrease after day 7. At the end of the experiment, there was no significant difference in viability and functionality between the scaffolds and the control.
CONCLUSION: In this initial study, porogen particles were used to modify the scaffolds produced from the novel polymer. Although there was no significance against the control in functionality and viability, the demonstrable attachment on scanning electron microscopy suggest potential roles for this polymer and in particular for scaffolds made with glucose particles in liver tissue engineering.
|Hussamuddin Adwan; Barry Fuller; Clare Seldon; Brian Davidson; Alexander Seifalian|
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|Type: Journal Article; Research Support, Non-U.S. Gov't Date: 2012-04-24|
|Title: Journal of biomaterials applications Volume: 28 ISSN: 1530-8022 ISO Abbreviation: J Biomater Appl Publication Date: 2013 Aug|
|Created Date: 2013-08-02 Completed Date: 2014-02-26 Revised Date: 2014-08-11|
Medline Journal Info:
|Nlm Unique ID: 8813912 Medline TA: J Biomater Appl Country: England|
|Languages: eng Pagination: 250-61 Citation Subset: IM|
|APA/MLA Format Download EndNote Download BibTex|
Glucose / chemistry
Hep G2 Cells
Liver / cytology*
Nanocomposites / chemistry*, ultrastructure
Organosilicon Compounds / chemistry*
Polyesters / chemistry*
Polyurethanes / chemistry*
Sodium Bicarbonate / chemistry
Sodium Chloride / chemistry
Tissue Engineering / methods
Tissue Scaffolds / chemistry*
|0/Organosilicon Compounds; 0/Polyesters; 0/Polyurethanes; 0/polyhedraloligosilsesquioxane; 24980-41-4/polycaprolactone; 7647-14-5/Sodium Chloride; 8MDF5V39QO/Sodium Bicarbonate; 97343-15-2/polyetherurethane urea; IY9XDZ35W2/Glucose|
Journal ID (nlm-ta): J Biomater Appl
Journal ID (iso-abbrev): J Biomater Appl
Journal ID (publisher-id): JBA
Journal ID (hwp): spjba
Publisher: SAGE Publications, Sage UK: London, England
© The Author(s) 2012 Reprints and permissions: sagepub.co.uk/journalsPermissions.nav
epub-ppub publication date: Month: 8 Year: 2013
Print publication date: Month: 8 Year: 2013
Volume: 28 Issue: 2
First Page: 250 Last Page: 261
PubMed Id: 22532408
Publisher Id: 10.1177_0885328212445404
|Modifying three-dimensional scaffolds from novel nanocomposite materials using dissolvable porogen particles for use in liver tissue engineering|
1University Department of Surgery, University College London, Royal Free
Hospital, London, UK
2Centre for Hepatology, University College London, Royal Free Hospital,
|Correspondence: Hussamuddin Adwan, University Department of Surgery,
University College London, Royal Free Hospital, London, UK. Email: email@example.com
Deaths from chronic liver disease (CLD) have increased by eight times in men and seven times in women over the past three decades, while the immediate mortality of acute liver disease (ALD) is in the range of 25–50%, patients with fulminant hepatic failure usually die without transplantation.1,2 Liver transplantation remains the only effective treatment for ALD and CLD, but many patients on the liver transplant list die whilst waiting for a graft. In the UK alone, between 1 April 2006 and 31 March 2007, there was a total of 1199 patients awaiting transplantation, of which only 649 patients (54%) received transplantation while 99 patients died (8%).3 Thus, bioartificial liver (BAL) tissue-engineered replacements could have a huge impact on the outcome of liver failure. Despite many on-going clinical trials into a number of BAL devices, none of them has been approved for clinical practice.4, bibr5-0885328212445404, bibr6-0885328212445404, bibr7-0885328212445404, bibr8-0885328212445404, bibr9-0885328212445404, bibr10-0885328212445404, bibr11-0885328212445404, bibr12-0885328212445404–13
The importance of polymeric matrices in the process of developing three-dimensional (3D) scaffolds is further highlighted by the fact that hepatocytes are attachment-dependent and lose their liver-specific function without optimal media and extracellular matrix (ECM) composition and cell-cell contacts.14, bibr15-0885328212445404, bibr16-0885328212445404, bibr17-0885328212445404, bibr18-0885328212445404, bibr19-0885328212445404, bibr20-0885328212445404–21 It was observed that the 3D matrix architecture influences the function and differentiation of liver cells in vitro. Hence, combining cell transplantation with 3D, highly porous polymeric matrices became an appealing concept.20,22, bibr23-0885328212445404–24 Therefore, the search continues to find the ideal polymer that would allow a high density of hepatocytes to maintain their viability and function and encourage neo-tissue formation. It has been agreed that the ideal scaffold should be biocompatible and highly porous with more controllable pore size ranging from 200 to 400 µm.7,9, bibr10-0885328212445404, bibr11-0885328212445404, bibr12-0885328212445404–13,21,25, bibr26-0885328212445404, bibr27-0885328212445404, bibr28-0885328212445404, bibr29-0885328212445404, bibr30-0885328212445404, bibr31-0885328212445404, bibr32-0885328212445404, bibr33-0885328212445404, bibr34-0885328212445404, bibr35-0885328212445404, bibr36-0885328212445404, bibr37-0885328212445404, bibr38-0885328212445404, bibr39-0885328212445404, bibr40-0885328212445404–41
Our laboratory has developed a novel nanocomposite biodegradable scaffold namely POSS-modified polycaprolactone urea urethane (PU) made by integrating Polyhedral Oligomeric Silsesquioxane® (POSS®) [a trademark of Hybrid Plastics (www.hybridplastics.com)], a cytocompatible polymer nanofiller with poly-ɛ-caprolactone (PCL), a biodegradable and nontoxic aliphatic polyester, that can produce highly porous scaffolds.42, bibr43-0885328212445404, bibr44-0885328212445404, bibr45-0885328212445404, bibr46-0885328212445404, bibr47-0885328212445404, bibr48-0885328212445404–49
This study examined the suitability of this novel polymer and its porogen modifications as potential scaffolds for bioengineered liver. The architecture and porosity of the new scaffolds were examined under scanning electron microscopy (SEM) and the anchorage, viability and functionality of seeded hepatocytes were studied on these novel scaffolds in a static culture using SEM and a number of viability and functionality assays.
Discs of polymer were formed by spreading the polymer at 15% concentration in solvent over Melinex sheets supported by stainless steel plates, coagulated by slow immersion in distilled water at room temperature and cut (the polymer attached to the Melinex sheet as PMS) at 15-mm diameter for use into 24-well tissue culture plates (TCPs). Shaped PMS pieces were kept moist and placed in covered glass Petri dishes, autoclaved and kept sterile until needed; 15 mm discs from Melinex sheets alone (Melinex) and normal TCPs were used as control.
The polymer (PU) at 10% concentration in solvent and three different modifications were made by adding porogens to PU at 1:1 weight ratio to produce four different scaffolds. The combined polymer and porogens were mixed manually then on a horizontal rotator for 1–2 h to produce a polymer with glucose (PG), sodium bicarbonate (PB) and with sodium chloride (PN); 15-mm discs were made by coagulating a 4.5–5 g spread of the mixtures into 5.5 cm diameter glass Petri dishes in distilled water overnight. Each of the four mixtures was coagulated in a dedicated water bath that was changed prior to cutting to shape four times lasting 30 min each time. The discs were then shaved off from two opposite sides to allow more contact with culture media. Scaffolds were kept moist, sealed in glass Petri dishes, and autoclaved.
HepG2 cells were cultured in growth medium (GM) made of DMEM+GlutaMAX™ Media (GIBCO®, Invitrogen™) with 10% foetal bovine serum (GIBCO®, Invitrogen™) and PenStrep at concentration of 100 Unit + 100 µg/ml of penicillin and streptomycine, respectively (10,000 Unit/ml penicillin and 10,000 µg/ml streptomycin, GIBCO®, Invitrogen™).50 GM was changed over the culture every 3–4 days and the cells were passaged at 60–80% confluence.
The scaffolds were covered with GM in 24-well TCPs (Costar®, Corning Inc.) and incubated at 37℃ and 5% CO2 overnight prior to moving them to a fresh 24-well plates for cell seeding. A 0.1 ml of homogenized HepG2 cells in GM at 10 × 104 cells/100 µl calculated using a haemocytometer were injected into each of the scaffolds and left to settle for 15–30 min, then topped up with 0.9 ml GM and incubated for 24 h. They were then carefully transferred into a pre-prepared 24-well plates with four wells already seeded with 10 × 104 cells/ml of GM and kept in similar conditions to the seeded scaffolds as control in TCPs. All wells were topped up to 2 ml of GM and incubated at 37℃ and 5% CO2. The day when the seeded 3D scaffolds were transferred into the pre-prepared wells was counted as day zero. Initial naked eye observation was used to assess the adequacy of the seeding process and further confirmation was made by comparing fluorescence intensity (FI) percentage difference on alamarBlue assay from randomly selected seeded scaffolds and from control in TCP on day 1.
An estimate of porosity was calculated by the formula:
|Percentage Porosity =(Vol.Solvent+Vol.Porogen)×100T.Vol.Polymer|
Pore sizes, pore wall thickness, inter-pore communications and hepatocytes anchorage, proliferation and cell-cell attachments were evaluated and described using SEM digital photography at 40, 320, 640 and 1250 times magnifications. Samples were fixed in 1.5% glutaraldehyde for a minimum of 2 h, washed with several changes of phosphate-buffered saline and postfixed using 1% osmium tetroxide/1.5% potassium ferricyanide for 12 h. Samples were then washed with distilled water and dehydrated through graded alcohols. Control samples were fixed using graded alcohol dehydration starting at 70%. All samples were then attached to aluminium stubs with double-sided sticky tabs (TAAB) and then coated with gold using an SC500 (EMScope) sputter coater before being examined and photographed using a Philips 501 scanning electron microscope.
HepG2 metabolic activities, proliferation and growth and scaffold cytotoxicity were assessed using alamarBlue® assay (Molecular Probes®, Invitrogen®) on days 1, 3, 7 and 14. A standard curve was worked out experimentally which suggested 4 h incubation period for the HepG2 cell line to be the optimum timing to measure the FI for alamarBlue®. Further quantification of the cell-line proliferation was made by quantitating double-stranded DNA (dsDNA) using PicoGreen® assay (Quant-iT™ PicoGreen® dsDNA Assay Kit, Molecular Probes®, Invitrogen®) on culture D10 of experiments on PMS and on culture D7 and D14 of experiments on the 3D scaffolds.
FI was measured using a fluorescence plate reader (Fluoroskan Ascent® FL, and Ascent Software, Thermo Labsystems, Helsinki, Finland) at 530 nm excitation wavelength and 620 nm emission wavelength for alamarBlue® and at 485 nm excitation and 538 nm emission for PicoGreen®. We used the means of the actual FI measurements in plotting for the graphs and charts and the percentage difference was calculated from the following equation:
|Percentage Difference=FI of the tested sample×100FI of the control sample|
Albumin secretion from 3D scaffolds and their control in TCP were measured using Human Albumin ELISA Quantification Kit (Bethyl Laboratories, Inc., Montgomery, USA) using manufacturer’s protocol.
Modular analytics clinical chemistry system (Roche Diagnostics, Basel, Switzerland) was used to measure urea and aspartate transferase (AST) levels in the GM supernatant from 3D scaffolds and their control in TCP.
GraphPad PRISM® Version 5.0 (GraphPad Software, Inc., San Diego, USA) was used for statistical analysis and graph illustration. Unless stated otherwise, samples were made in quadruplets (n4) and statistical analysis was performed at 95% CI. Data was initially analysed using Kruskal-Wallis test and further specific pairwise post-hoc comparisons were carried out as needed using Dunn's Multiple Comparison test or Mann Whitney U test.51
Using the percentage porosity equation, we estimated the porosity of PG, PB and PN to be around 95% while that of the PU to be around 90%. The scaffold made by using glucose as porogen (PG) demonstrated a better architecture than the other scaffolds by means of better porosity with most of pore sizes above 200 µm (ranging from 100–350 µm), highly communicative porous structure and pore walls as thin as 1.2–12 µm. The other scaffolds were relatively far off the ideal scaffold architecturally. PU scaffolds had a large pore size ranging from 500 µm–2 mm, distinctly thick pore walls towards the surface of the polymer (170–650 µm) but thinner towards the lower half of the polymer (10–100 µm), with limited inter-pore communications, and pores were lined with clusters of spherical bodies ranging in size from 2 to 5 µm. PB and PN scaffolds had extremely variable pore sizes (20–750 µm and 150 µm–1.5 mm, respectively; Figure 1).
Complete seeding in TCP and on 2D scaffolds was observed, but a small fraction of the homogenised solution leaked from the shaved sides of the 3D scaffolds. A general estimate of this leak was extrapolated by comparing FI percentage difference on alamarBlue® assay on day 1.
On culture D8, near-complete hepatocyte confluence was demonstrated on 2D (monolayer) culture on PMS comparable to control on Melinex (Figure 2). Hepatocytes morphology, polyhedral characterisation, cell-cell and cell-matrix attachment were observed on higher SEM magnification on 2D PMS and in 3D scaffolds with numerous cells attached to the scaffolds’ porous structures (Figure 3 and 4). Cells were observed to form healthier colonies with smoother surfaces and higher incidence of cell aggregates on PG scaffolds when compared with other scaffolds (Figure 4).
The mean FI emission from control in TCP was higher than from control in Melinex throughout on alamarBlue® assay and on culture D10 on PicoGreen® assay, but the differences were not significant and both control produced comparable graphs with matching trends on alamarBlue® suggesting that Melinex is a suitable alternative to compare with PMS in SEM evaluation. Culture on PMS demonstrated progressive FI emission in alamarBlue® assay and on culture D8 mean FI measured was significantly higher than on D2 (88.33 vs. 52.65 U/L, respectively, Mann-Whitney p = 0.0286). Although the mean FI measured from Melinex was significantly higher than from PMS on two occasions, culture D3 and D8 (Kruskal-Wallis p = 0.0207 and 0.0218, respectively; Dunn's multiple comparison test p < 0.05 for each), they produced graphs with similar trends (Graph 1(a)). On culture D10 there was little difference in mean FI emission between PMS and Melinex on PicoGreen® assay (46.74 vs. 50.65 U/L, respectively, FI percentage difference 92.28, Mann-Whitney p = 0.3429), which was not in line with the much higher difference found on alamarBlue® assay (50.94 vs. 98.40 U/L, respectively, FI percentage difference 51.77; Graphs 1(a) and 2(a).
All 3D scaffolds cultures demonstrated progressive FI emission on alamarBlue® assay up to the end of the experiment on culture D14 and the higher mean FI emission from control in TCP losses its significance when compared to most of the scaffolds on culture D14 (Graph 1(b)). There was a significantly higher mean FI emission from control in TCP than from most of the scaffolds on culture D7, but the higher mean FI emission from control in TCP on PicoGreen® assay showed a narrower non-significant difference (i.e. higher FI percentage difference) than on alamarBlue® on culture D7 (Graph 2). There was a clear increase in FI emission on PicoGreen® from all the scaffolds on culture D14 as compared to D7 (Graph 2(b)).
Mean AST production was notably low across the board on culture D1, D3 and D14, with a transient relative increase from control in TCP and from PG scaffold on D7 when compared to other scaffolds (Graph 3(a)).
There was a significant increase in albumin production from all 3D scaffolds and their control in TCP on culture D7 and D14 as compared to D1 (Kruskal-Wallis p = 0.0030; Dunn's multiple comparison test p < 0.05), suggesting the progressive proliferation of viable hepatocytes in all the scaffolds. Albumin production peaked on culture D7 across all samples but declined across the board at the end of the experiment on D14. The decline was much greater from control in TCP than from the scaffolds of which PG showed the smallest decline (Graph 3(b)).
A significant increase of urea synthesis on culture D7 and D14 from all scaffolds and the control in TCP was observed in comparison to urea synthesis on D1 (Kruskal-Wallis p = 0.0006; Dunn's multiple comparison test p < 0.05; Graph 3(c)). Pairwise post-hoc comparison suggested a significantly higher urea synthesis on culture D14 from control in TCP in comparison to urea synthesis from PG, PB and PU scaffolds (Mann Whitney Test p = 0.0408, 0.0294 and 0.0294 for each, respectively).
This is the first study to demonstrate the maintenance of viable and functional hepatocytes on a novel nanocomposite polymer i.e. POSS-modified polycaprolactone urea urethane. We opted to use human HepG2 cell line for their similar morphology to adult primary hepatocytes, their tendency to attach and their albumin-synthesizing capacity, although their ammonia detoxification and mixed function oxidase activities were very poor.52 These cells also undergo cell division (which is not the case for primary hepatocytes) and therefore allowed us to assess the potential scaffolds for their ability to support increasing cell numbers. This has relevance to the future hope of being able to use stem cells or partially committed progenitor cells at scale-up to provide liver support systems. On examining polymer-coated Melinex disks (PMS) and control on Melinex disks and in TCP, there was a statistically significant higher FI emission from control in TCP and to some extent from control on Melinex than from PMS on both alamarBlue and PicoGreen; however, they all exhibited a similar trend with a matching trend on alamarBlue. This would suggest that the polymer might have a dampening effect on the fluorescence signal. In line with this possibility is the observation that the percentage difference between PMS and TCP on day 10 on PicoGreen assay was 81.17%, nearly double that of alamarBlue, which was 48.54%, for the same day and samples. Additionally, the SEM demonstrated near-complete confluence of hepatocytes by culture D8 and it showed clear cell-cell and cell-matrix attachment on PMS. The fact that hepatocytes retained their polyhedral shape and have less overriding cells when compared with Melinex further suggests that FI emission on alamarBlue assay may not have reflected the actual cellular viability and as such may not have been the most appropriate assay for this polymer. These observations were taken into account when planning for and analysing further experiments on 3D scaffolds.
The novel use of porogens in the making of these 3D scaffolds depends on the choice of non-toxic particles that would dissolve in water during the polymer coagulation process leaving behind a porous structure with more controlled range of pore sizes. Of all the three particles chosen, glucose is the one that would be the most inert for hepatocytes if it did not dissolve completely. Although all 3D scaffolds exhibit striking architectural differences, PG scaffolds showed more favouring architecture for the narrower range of their pore sizes, numerous interpore communications and their relatively thin interpore walls. While SEM examination demonstrated cell attachment on all scaffolds, hepatocytes seeded on PG scaffolds tend to have a smoother outline.
In all the experiments carried out to evaluate the viability and the functionality of the seeded hepatocytes, control in TCP had a higher rate of FI emissions in comparison to emissions from the scaffolds. However, lack of significance in the difference between control in TCP and scaffolds in the presence of demonstrable progressive increase in albumin, urea and AST production across all the scaffolds suggest that hepatocytes maintained viability and functionality within these scaffolds. A number of observations in this study suggest continuing and progressive proliferation, viability and functionality of hepatocytes when seeded onto these scaffolds, especially onto PG scaffolds. These observations include the progressive increase in cell population as evidenced by a higher FI emission on culture D14 than on D7 on PicoGreen; the clear discrepancy between FI emissions and FI percentage difference on PicoGreen when compared to that from alamarBlue; the potential dumping effect of the new polymer on FI emissions for alamarBlue assay suggested by experiments on PMS and the clear SEM demonstration of cell attachments to the porous structures of the scaffolds.
A clearer demonstration was noted with albumin secretion when the significant increase in its production on culture D7 from control in TCP was followed by a steep decline a week later, which was not matched by an equivalent reduction from the scaffolds. The scaffolds, on the other hand, continued to demonstrate progressive production of albumin throughout the experiment. Although HepG2 cells are not known for their urea synthesis ability, there was a progressive secretion at a relatively similar rate from all the scaffolds throughout the experiment. As the native polymer is based on a urea compound, its exact influence on urea level is difficult to predict and remains to be further investigated. The use of AST in evaluating in vitro hepatocyte culture albeit novel is not without difficulty in interpreting its significance. When we decided to use it we anticipated a high level to be predictive of a higher rate of hepatocyte damage. The production of AST, however, gave a similar graph shape to that of albumin secretion. On one hand it was anticipated that AST would be higher from control in TCP as cell proliferation in 2D culture is more likely to reach confluence sooner than on 3D scaffolds. On the other hand, albumin secretion peaked as AST secretion reached its highest level from control in TCP. Perhaps the sharp decline in both AST and albumin secretion from control in TCP indicated that cells in TCP had reached their maximum potential, while the steady progressive production of albumin and AST from the scaffolds was suggestive of the scaffolds’ potential to support hepatocytes’ functionality and viability in culture for a longer period and this needs further evaluation. It was notable that scaffolds made with glucose (PG) had a relatively higher rate of albumin and AST production when compared to the other scaffolds.
We found that the use of dissolvable porogen particles in developing 3D scaffolds from POSS-modified polycaprolactone urea urethane polymer modifies the scaffolds’ properties and allows liver cell attachment and functionality in particular when combined with glucose as a porogen. However, this is a new polymer and more work is needed to establish the best method for leaching and coagulation and the most efficient way to assess cell count and viability within the scaffold structure. We think that this polymer when combined with glucose has the potential to be used in liver tissue engineering.
Sample preparation and SEM examination and photography were provided by the Electron Microscopy Unit at Royal Free Hospital, Hampstead and University College London.
With help from the Department of Clinical Biochemistry at Royal Free Hampstead NHS Trust, London, The Liver Group at the Centre for Hepatology, Department of Medicine, Royal Free & University College Medical School, London. The Plate Washer and Plate Reader were provided by the Liver Group Laboratories, Centre for Hepatology, Royal Free and University College Medical School, London).
This project was carried out as part of my MSc Surgical Science degree at the Departments of Anatomy and Developmental Biology and Surgery at University College London, UK.
|1.||Facts about liver disease, http://www.britishlivertrust.org. uk/data/5/pages/2 aspx?pid=280 (2008). (accessed 31 January 2008).|
|2.||Standards for solid organ transplantation in the United Kingdom, http://www.bts.org.uk/Forms/standards%20document%20edition%202%20-%20final pdf (2003 July). (accessed 31 January 2008).|
|3.||Transplant activity in the UK, http://www.uktransplant. org.uk/ukt/statistics/transplant_activity_report/current_activity_reports/ukt/transplant_activity_uk_2006-2007 pdf (2007 August). (accessed 31 January 2008).|
|4.||Vienken J,Christmann H. How can liver toxins be removed? Filtration and adsorption with the Prometheus system. Ther Apher DialYear: 2006; 10(2): 125–13116684213|
|5.||Laleman W,Wilmer A,Evenepoel P,et al. Review article: non-biological liver support in liver failure. Aliment Pharmacol TherYear: 2006; 23(3): 351–36316422994|
|6.||Sen S,Williams R,Jalan R. Emerging indications for albumin dialysis. Am J GastroenterolYear: 2005; 100(2): 468–47515667509|
|7.||Rozga J. Liver support technology—an update. XenotransplantationYear: 2006; 13(5): 380–38916925661|
|8.||Mitzner S,Klammt S,Stange J,et al. Albumin regeneration in liver support-comparison of different methods. Ther Apher DialYear: 2006; 10(2): 108–11716684211|
|9.||Jalan R,Sen S,Williams R. Prospects for extracorporeal liver support. GutYear: 2004; 53(6): 890–89815138219|
|10.||Pryor HI,Vacanti JP. The promise of artificial liver replacement. Front BiosciYear: 2008; 13: 2140–215917981698|
|11.||Gerlach JC,Zeilinger K,Patzer Ii JF. Bioartificial liver systems: why, what, whither?. Regen MedYear: 2008; 3(4): 575–59518588477|
|12.||Faenza S,Baraldi O,Bernardi M,et al. Mars and Prometheus: our clinical experience in acute chronic liver failure. Transplant ProcYear: 2008; 40(4): 1169–117118555140|
|13.||Dethloff T,Tofteng F,Frederiksen HJ,et al. Effect of Prometheus liver assist system on systemic hemodynamics in patients with cirrhosis: a randomized controlled study. World J GastroenterolYear: 2008; 14(13): 2065–207118395908|
|14.||Fiegel HC,Havers J,Kneser U,et al. Influence of flow conditions and matrix coatings on growth and differentiation of three-dimensionally cultured rat hepatocytes. Tissue EngYear: 2004; 10(1–2): 165–17415009942|
|15.||Takashi H,Katsumi M,Toshihiro A. Hepatocytes maintain their function on basement membrane formed by epithelial cells. Biochem Biophys Res CommunYear: 2007; 359(1): 151–15617531195|
|16.||Miyazawa M,Torii T,Toshimitsu Y,et al. Hepatocyte dynamics in a three-dimensional rotating bioreactor. J Gastroenterol HepatolYear: 2007; 22(11): 1959–196417914977|
|17.||Michalopoulos GK. Liver regeneration. J Cell PhysiolYear: 2007; 213(2): 286–30017559071|
|18.||Kim SS,Utsunomiya H,Koski JA,et al. Survival and function of hepatocytes on a novel three-dimensional synthetic biodegradable polymer scaffold with an intrinsic network of channels. Ann SurgYear: 1998; 228(1): 8–139671060|
|19.||Allen JW,Bhatia SN. Engineering liver therapies for the future. Tissue EngYear: 2002; 8(5): 725–73712459052|
|20.||Fiegel HC,Kaufmann PM,Bruns H,et al. Hepatic tissue engineering: from transplantation to customized cell-based liver directed therapies from the laboratory. J Cell Mol MedYear: 2008; 12(1): 56–6618021311|
|21.||Torok E,Pollok JM,Ma PX,et al. Hepatic tissue engineering on 3-dimensional biodegradable polymers within a pulsatile flow bioreactor. Dig SurgYear: 2001; 18(3): 196–20311464009|
|22.||Sellaro TL,Ravindra AK,Stolz DB,et al. Maintenance of hepatic sinusoidal endothelial cell phenotype in vitro using organ-specific extracellular matrix scaffolds. Tissue EngYear: 2007; 13(9): 2301–231017561801|
|23.||Zavan B,Brun P,Vindigni V,et al. Extracellular matrix-enriched polymeric scaffolds as a substrate for hepatocyte cultures: in vitro and in vivo studies. BiomaterialsYear: 2005; 26(34): 7038–704515993941|
|24.||Bruns H,Kneser U,Holzhuter S,et al. Injectable liver: a novel approach using fibrin gel as a matrix for culture and intrahepatic transplantation of hepatocytes. Tissue EngYear: 2005; 11(11–12): 1718–172616411817|
|25.||Vienken J,Christmann H. How can liver toxins be removed? Filtration and adsorption with the Prometheus system. Ther Apher DialYear: 2006; 10(2): 125–13116684213|
|26.||Laleman W,Wilmer A,Evenepoel P,et al. Review article: non-biological liver support in liver failure. Aliment Pharmacol TherYear: 2006; 23(3): 351–36316422994|
|27.||Sen S,Williams R,Jalan R. Emerging indications for albumin dialysis. Am J GastroenterolYear: 2005; 100(2): 468–47515667509|
|28.||Mitzner S,Klammt S,Stange J,et al. Albumin regeneration in liver support-comparison of different methods. Ther Apher DialYear: 2006; 10(2): 108–11716684211|
|29.||Stadlbauer V,Jalan R. Acute liver failure: liver support therapies. Curr Opin Crit CareYear: 2007; 13(2): 215–22117327745|
|30.||Planchamp C,Vu TL,Mayer JM,et al. Hepatocyte hollow-fibre bioreactors: design, set-up, validation and applications. J Pharm PharmacolYear: 2003; 55(9): 1181–119814604461|
|31.||Jasmund I,Bader A. Bioreactor developments for tissue engineering applications by the example of the bioartificial liver. Adv Biochem Eng BiotechnolYear: 2002; 74: 99–10911991185|
|32.||Allen JW,Hassanein T,Bhatia SN. Advances in bioartificial liver devices. HepatologyYear: 2001; 34(3): 447–45511526528|
|33.||Chamuleau RA. Artificial liver support in the third millennium. Artif Cells Blood Substit Immobil BiotechnolYear: 2003; 31(2): 117–12612751830|
|34.||Hoque ME,Mao HQ,Ramakrishna S. Hybrid braided 3-D scaffold for bioartificial liver assist devices. J Biomater Sci Polym EdYear: 2007; 18(1): 45–5817274450|
|35.||Kaufmann PM,Heimrath S,Kim BS,et al. Highly porous polymer matrices as a three-dimensional culture system for hepatocytes: initial results. Transplant ProcYear: 1997; 29(4): 2032–20349193513|
|36.||Kaufmann PM,Kneser U,Fiegel HC,et al. Long-term hepatocyte transplantation using three-dimensional matrices. Transplant ProcYear: 1999; 31(4): 1928–192910391802|
|37.||Kaufmann PM,Heimrath S,Kim BS,et al. Highly porous polymer matrices as a three-dimensional culture system for hepatocytes. Cell TransplantYear: 1997; 6(5): 463–4689331497|
|38.||Mooney DJ,Park S,Kaufmann PM,et al. Biodegradable sponges for hepatocyte transplantation. J Biomed Mater ResYear: 1995; 29(8): 959–9657593039|
|39.||Uyama S,Kaufmann PM,Kneser U,et al. Hepatocyte transplantation using biodegradable matrices in ascorbic acid-deficient rats: comparison with heterotopically transplanted liver grafts. TransplantationYear: 2001; 71(9): 1226–123111397954|
|40.||Davis MW,Vacanti JP. Toward development of an implantable tissue engineered liver. BiomaterialsYear: 1996; 17(3): 365–3728745334|
|41.||Kulig KM,Vacanti JP. Hepatic tissue engineering. Transpl ImmunolYear: 2004; 12(3–4): 303–31015157923|
|42.||Madbouly SA,Otaigbe JU,Nanda AK,et al. Rheological behavior of POSS/polyurethane-urea nanocomposite films prepared by homogeneous solution polymerization in aqueous dispersions. MacromoleculesYear: 2007; 40(14): 4982–4991|
|43.||Hule RA,Pochan D. Polymer Nanocomposites for biomedical applications. MRS BulletinYear: 2007; 32: 354–358|
|44.||Neumann D,Fisher M,Tran L,et al. Synthesis and characterization of an isocyanate functionalized polyhedral oligosilsesquioxane and the subsequent formation of an organic-inorganic hybrid polyurethane. J Am Chem SocYear: 2002; 124(47): 13998–1399912440890|
|45.||Kannan RY,Salacinski HJ,Ghanavi JE,et al. Silsesquioxane nanocomposites as tissue implants. Plast Reconstr SurgYear: 2007; 119(6): 1653–166217440337|
|46.||Kannan RY,Salacinski HJ,Sales KM,et al. The endothelialization of polyhedral oligomeric silsesquioxane nanocomposites: an in vitro study. Cell Biochem BiophysYear: 2006; 45(2): 129–13616757813|
|47.||Kannan RY,Salacinski HJ,Odlyha M,et al. The degradative resistance of polyhedral oligomeric silsesquioxane nanocore integrated polyurethanes: an in vitro study. BiomaterialsYear: 2006; 27(9): 1971–197916253324|
|48.||Alobaid N,Salacinski HJ,Sales KM,et al. Nanocomposite containing bioactive peptides promote endothelialisation by circulating progenitor cells: an in vitro evaluation. Eur J Vasc Endovasc SurgYear: 2006; 32(1): 76–8316466940|
|49.||Goh YQ,Ooi CP. Fabrication and characterization of porous poly(L-lactide) scaffolds using solid-liquid phase separation. J Mater Sci Mater MedYear: 2008; 19(6): 2445–245218219558|
|50.||Yamashita Y,Shimada M,Tsujita E,et al. Polyurethane foam/spheroid culture system using human hepatoblastoma cell line (Hep G2) as a possible new hybrid artificial liver. Cell TransplantYear: 2001; 10(8): 717–72211814114|
|51.||Petrie A,Sabin C. Medical statistics at a glance, 2nd edMalden, MA: Blackwell, Year: 2005|
|52.||Harimoto N,Taketomi A,Kitagawa D,et al. The newly established human hepatocyte cell line: application for the bioartificial liver. J HepatolYear: 2005; 42(4): 557–56415763342|
Keywords: POSS-modified polycaprolactone urea urethane, nanocomposite polymers, hepatocytes, tissue engineering, scaffolds, porogens, HepG2.
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