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Modifying three-dimensional scaffolds from novel nanocomposite materials using dissolvable porogen particles for use in liver tissue engineering.
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MedLine Citation:
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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Publication Detail:
Type:  Journal Article; Research Support, Non-U.S. Gov't     Date:  2012-04-24
Journal Detail:
Title:  Journal of biomaterials applications     Volume:  28     ISSN:  1530-8022     ISO Abbreviation:  J Biomater Appl     Publication Date:  2013 Aug 
Date Detail:
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    
Other Details:
Languages:  eng     Pagination:  250-61     Citation Subset:  IM    
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MeSH Terms
Cell Adhesion
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*
Reg. No./Substance:
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

From MEDLINE®/PubMed®, a database of the U.S. National Library of Medicine

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Journal Information
Journal ID (nlm-ta): J Biomater Appl
Journal ID (iso-abbrev): J Biomater Appl
Journal ID (publisher-id): JBA
Journal ID (hwp): spjba
ISSN: 0885-3282
ISSN: 1530-8022
Publisher: SAGE Publications, Sage UK: London, England
Article Information
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© The Author(s) 2012 Reprints and permissions:
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
ID: 4107826
DOI: 10.1177/0885328212445404
Publisher Id: 10.1177_0885328212445404

Modifying three-dimensional scaffolds from novel nanocomposite materials using dissolvable porogen particles for use in liver tissue engineering
Hussamuddin Adwan1
Barry Fuller1
Clare Seldon2
Brian Davidson1
Alexander Seifalian1
1University Department of Surgery, University College London, Royal Free Hospital, London, UK
2Centre for Hepatology, University College London, Royal Free Hospital, London, UK
Correspondence: Hussamuddin Adwan, University Department of Surgery, University College London, Royal Free Hospital, London, UK. Email:


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, bibr12-088532821244540413

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, bibr20-088532821244540421 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, bibr23-088532821244540424 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, bibr12-088532821244540413,21,25, 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, bibr40-088532821244540441

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 (], 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, bibr48-088532821244540449

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.

Polymer preparation, coagulation and construction
Making 2D discs

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.

Making 3D scaffolds

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.

Cell culturing conditions and cell seeding
Cell culturing, passaging and maintenance

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.

HepG2 cell seeding

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.

Characterisation of the scaffolds and the seeded hepatocytes
Porosity calculation

An estimate of porosity was calculated by the formula:

[Formula ID: disp-formula1-0885328212445404]
Percentage Porosity   =(Vol.Solvent+Vol.Porogen)×100T.Vol.Polymer

Scanning electron microscopy

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.

Assessment of hepatocytes viability, proliferation and functionality
AlamarBlue® and PicoGreen® assays

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:

[Formula ID: disp-formula2-0885328212445404]
Percentage Difference=FI of the tested sample×100FI of the control sample

Measurement of aspartate transferase, albumin and urea in supernatant medium
Human albumin ELISA assay

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.

Urea synthesis and aspartate transferase

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.

Statistical analysis and software

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

Scaffolds characterisation

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).

Cell seeding and cell characterisation

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).

Cell viability, proliferation and functionality assessments
AlamarBlue® and PicoGreen® assays

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)).

AST secretion

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)).

Albumin ELISA secretion

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)).

Urea synthesis

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, uk/data/5/pages/2 aspx?pid=280 (2008). (accessed 31 January 2008).
2. Standards for solid organ transplantation in the United Kingdom, pdf (2003 July). (accessed 31 January 2008).
3. Transplant activity in the UK, http://www.uktransplant. 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


[Figure ID: fig1-0885328212445404]
Figure 1. 

Scanning electron microscopy (SEM) at (1) 40 and (2) 320 times magnifications of transverse sections of the 3D scaffolds: (a) polycaprolactone urea urethane (PU), (b) polymer with glucose (PG), (c) sodium bicarbonate (PB) and (d) sodium chloride (PN). The pores and the wall thickness are largest in PU and finest in PB while PN shows a distinct layer of fine pores on top of a layer of much larger pore sizes. Only PG demonstrated a nearly uniformal mixture of pore sizes which is neither very large nor very small, along with a narrower range of wall thickness and more interpore communications. Although PB at higher magnification demonstrated higher interpore communications, the overall pore sizes were either too small or too large, rendering their support to cells and their influence on hepatocytes’ proliferation less uniformal and hence less predictable.

[Figure ID: fig2-0885328212445404]
Figure 2. 

Scanning electron microscopy (SEM) at 80 times magnification on Day 5, 8 and 10 (1, 2 and 3, respectively) comparing hepatocytes’ confluence and proliferation on (a) PMS and (b) Melinex. The rate of proliferation of hepatocytes on PMS seems similar if not higher than on Melinex as indicated by the near complete cell confluence on Day 8 on PMS. The cracks noted between cell aggregates on PMS on Day 8 and 10 could be a combination of the alcohol dehydration process used to prepare the slides for SEM and an overlap of cell growth.

[Figure ID: fig3-0885328212445404]
Figure 3. 

Scanning electron microscopy (SEM) at 640 (a) and (b) and at 2500 magnifications (c) and (d) on culture Day 3 on PMS. HepG2 hepatocytes seem to retain their phenotypical hexagonal appearance. Cell-cell and cell-matrix attachments on PMS can also be observed especially around the peripheries of cell clusters and with more clarity in (d).

[Figure ID: fig4-0885328212445404]
Figure 4. 

Scanning electron microscopy (SEM) at 2500 magnification demonstrating cell-cell and cell-matrix attachment on culture Day 7 of HepG2 in the three-dimensional (3D) nanocomposite scaffolds: POSS-modified polycaprolactone urea urethane (PU) (a) and its porogen modifications, i.e. with glucose particles (PG) (b), with sodium bicarbonate particles (PB) (c) and with sodium chloride particles (PN) (d). The cell surface looks smoother and has less granulation in PU and in PG. The cracks within HepG2 sheets could have been from the alcohol dehydration process during sample preparation for SEM.

[Figure ID: fig5-0885328212445404]
Graph 1. 

Summary graphs representing the results of alamarBlue® assay: (a) Examining PMS in 2D cultures against two different controls, in Meliniex and in tissue culture plates (TCPs). Although fluorescence intensity (FI) emissions were higher from control in Melinex and in TCP than from PMS, there was little, if any, difference between the two controls and both controls exhibit a similar graph trend, rendering control in Melinx as a suitable alternative for control in TCP, especially for scanning electron microscope (SEM) examination. FI emission from PMS was significantly higher on culture D5 and D8 when compared to D1, suggesting PMS capacity to maintain hepatocytes for that period. Although FI emissions from control in TCP were significantly higher (*) than from PMS on culture D2, D5 and D10 (mean FI percentage difference was 45.22, 57.79 and 48.54, respectively), and FI emissions from control in Melinex were significantly higher (**) than from PMS on culture D3 and D8 (mean FI percentage difference was 55.89 and 58.89, respectively), the graph trend of FI emissions exhibited from PMS is similar to that demonstrated by control in TCP and in Melinex. (b) Examining the three-dimensional (3D) scaffolds and their control in TCP, FI emissions from control in TCP were significantly higher than emissions from the scaffolds throughout the experiment, which could be explained by the leak of the homogenised cell solution at the beginning of the experiment (FI percentage difference of the means on culture D1 between TCP and polymer with glucose (PG), sodium bicarbonate (PB), sodium chloride (PN) and polycaprolactone urea urethane (PU) was 35.12, 19.31, 42.48 and 21.95, respectively). However, all 3D scaffolds continue to demonstrate FI emission on alamarBlue up to culture D14, suggesting their capacity to maintain hepatocytes for the length of the experiment. This is further supported by the reduction in the difference of FI emission (i.e. larger FI percentage difference) between most of the scaffolds and control in TCP (FI percentage difference of the means on culture D14 between TCP and PG, PB, PN and PU was 44.78, 54.33, 36.66 and 47.74, respectively).

[Figure ID: fig6-0885328212445404]
Graph 2. 

A bar chart and a graph representing PicoGreen assay reflecting the relative quantity of HepG2 cells in cultures as indicated by quantifying FI emissions of released cellular DNA’s following induced cell destruction. (a) Comparison between fluorescence intensity (FI) emission from PMS and control in tissue culture plates (TCP) and in Melinex on culture D10 (at the end of the initial experiment). Although, mean FI emission from PMS was lower than from control in Melinex and significantly lower than from control in TCP (46.74, 50.65 and 57.59 U/L respectively; Kruskal-Wallis p = 0.0183; Dunn’s multiple comparison test p < 0.05 for PMS vs. TCP), the difference between the three cultures on PicoGreen was much less than the difference found on alamarBlue (i.e. higher FI percentage difference: 92.28 for PMS vs. Melinex and 81.16 for PMS vs. TCP). (b) A graph comparing FI emissions from each of the 3D scaffolds with each other and with control in TCP on culture D7 and D14. Factoring in the initial low count of HepG2 cells at the beginning of the experiment (due to the small unquantifiable leak of the homogenised solution at the time of seeding), a higher but non-significant FI emission from control in TCP than from the scaffolds was anticipated. However, FI emissions were higher on culture D14 than on D7 across all the 3D scaffolds suggesting progressive increase in HepG2 cell count and the maintenance of viable cell culture for the duration of the experiment.

[Figure ID: fig7-0885328212445404]
Graph 3. 

Summary graphs representing aspartate transferase (AST), albumin and urea synthesis (a, b and c, respectively) from seeded 3D scaffolds on culture Day 1, 3, 7 and 14. AST is not commonly used to study static tissue culture. Unlike albumin and urea synthesis where a high level reflects progressive proliferation of functioning hepatocytes, a high AST level should indicate an increased number of damaged hepatocytes. Hence by simple deduction, continuous synthesis of AST requires progressive hepatocyte proliferation. This could explain the rapid decline following the initial steady rise. The coincidental rapid decline of albumin secretion from control in TCP detected on culture D14 after its initial increase on culture D7 would support this analogy (3.0, 14.125 and 8.0 U/L mean AST release vs. 680.81, 15,259 and 9467.95 ng/ml mean albumin secretion from control in TCP on culture D1, 7 and 14, respectively). The AST (a) and similarly albumin synthesis (b) exhibited plateau from 3D scaffolds after culture D7 would indirectly suggest progressive proliferation of functioning hepatocytes. This is further supported by the gradual increase in urea synthesis across all scaffolds (c). In all these experiments, AST, albumin secretion and urea synthesis were all higher from PG scaffolds when compared to other scaffolds (highest on culture D7). The higher levels detected from control in TCP possibly reflects the initial small unquantifiable loss of homogenised cell solution at the time of cell seeding into 3D scaffolds.

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Keywords: POSS-modified polycaprolactone urea urethane, nanocomposite polymers, hepatocytes, tissue engineering, scaffolds, porogens, HepG2.

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