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This article is part of the supplement: 22nd European Society for Animal Cell Technology (ESACT) Meeting on Cell Based Technologies

Open Access Meeting abstract

Study of a recombinant CHO cell line producing a monoclonal antibody by ATF or TFF external filter perfusion in a WAVE Bioreactor™

Marie-Françoise Clincke1, Carin Mölleryd1, Ye Zhang1, Eva Lindskog2, Kieron Walsh3 and Véronique Chotteau1*

Author Affiliations

1 School of Biotechnology, Animal Cell Technology Group, Royal Institute of Technology (KTH), SE-106 91 Stockholm, Sweden

2 GE Healthcare Bio-Sciences AB, Björkgatan 30, SE-75184 Uppsala, Sweden

3 GE Healthcare Bio-Sciences Corp, 14 Walk Up Drive, Westborough MA, 01581, USA

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BMC Proceedings 2011, 5(Suppl 8):P105  doi:10.1186/1753-6561-5-S8-P105

The electronic version of this article is the complete one and can be found online at: http://www.biomedcentral.com/1753-6561/5/S8/P105


Published:22 November 2011

© 2011 Clincke et al; licensee BioMed Central Ltd.

This is an open access article distributed under the terms of the Creative Commons Attribution License (http://creativecommons.org/licenses/by/2.0), which permits unrestricted use, distribution, and reproduction in any medium, provided the original work is properly cited.

Background

Major advantages of perfusion are high cell numbers and high total production in a relatively small size bioreactor. Moreover, perfusion is optimal when the product of interest is unstable or if the product yield is low. On the other hand, disadvantages are for example technical challenges originating from non-robust cell separation devices as well as sterility concerns from the more complex set-up needed.

In the present work, the use of a WAVE Bioreactor™ system 20/50 in perfusion mode with10 L disposable Cellbag™ bioreactors customized with two dip tubes in combination with disposable hollow fiber filters as external cell separating devices were investigated. A comparison between Alternating Tangential Flow (ATF) and Tangential Flow Filtration (TFF) was performed using a recombinant CHO cell line producing a monoclonal antibody (mAb) as a model system.

Materials and methods

A research cell line DHFR- CHO producing mAb was used. During expansion cultures in shake flasks, MTX selection pressure was performed but omitted in bioreactor. A WAVE Cellbag™ (10 L) containing two dip tubes (GE Healthcare) at 4L working volume was connected either to an ATF-2 device (Refine Technology, USA) or to a ReadyToProcess™ filter (TFF) via a Watson Marlow 620S pump. In both systems, the hollow fiber filters (HF), RTPCFP-2-E-4X2MS, GE Healthcare, Sweden, had 0.2 μm pore size, 1 mm lumen and 850 cm2 filter area. The pressure rising flow (ATF), the exhaust flow (ATF) and the recirculation flow rate (TFF) were 0.7 or 1 L/min. The set-points of DO, pH and temperature were 35 %, 7 and 37°C respectively. The agitation rate was varied between 20-26 rpm, 6-7° and 20-27 rpm, 6-8° for ATF and TFF respectively. O2 addition was performed in the headspace (20-100%) and the DO control was operated by varying the agitation.

The cells were cultivated in serum-free, animal-component free IS CHO CD XP medium (Irvine Scientific, USA) with hydrolysate, supplemented with 3 % of IS-CHO Feed-CD XP (Irvine Scientific, USA) and with 4 mM glutamine with a cell specific perfusion rate of 0.05 Reactor Volume/(day x 106 cells/mL). Supplementations of glucose or glutamine were performed according to cell need. The pH was controlled by adding 0.5 M Na2CO3 or pulsing CO2 into the headspace. The cell density, viability, pH, pCO2, concentrations of glucose, lactate, glutamine and ammonia were measured by Bioprofile FLEX (Nova Biomedical). Antifoam C (Sigma Aldrich, US) was added up to 50 ppm concentration in the bioreactor either by boost addition or by continuous pumping. The mAb concentration was measured by protein A HPLC.

Results

Cell density, viability and perfusion rate

Two perfusion experiments (ATF9 and ATF15) were conducted using ATF (Figure 1A) and one perfusion culture (TFF10) using TFF device (Figure 1B). In experiments ATF9 and TFF10, cell density was maintained between 20-30 x 106 cells/mL by daily cell bleeds for 2 weeks using one HF. Interestingly, in experiment ATF9, the use of an ATF flow rate of 0.7 L/min was not sufficient to remove bubbles entrapped in the HF resulting in a decrease in viability (93.5% vs. 97%). Therefore, from day 9, the flow rate was increased to 1 L/min, i.e. shear stress of 3400 s-1. Experiment ATF15 was performed at 1 L/min.

thumbnailFigure 1. Viable cell density (●, ○), viability (▲, △) and perfusion rate (■, □) in perfusion processes using ATF system (A) and TFF system (B). Closed symbols indicate the ATF9 perfusion experiment, whereas the open symbols represent the ATF15 and TFF10 perfusion experiments.

In experiment ATF15, a cell density of 132 x 106 cells/mL was reached after 10 days of culture of exponential growth. Reaching this density coincided with interruption of ATF function due to insufficient pressure to push the highly viscous cell broth, showing the limit of this system at this very high cell density when using a non-pressurisable disposable bioreactor. A batch culture was then carried out between days 13 and 20 (data not shown) after which perfusion was re-started. A maximal cell density of 123 x 106 cells/mL was obtained confirming the first observed maximal cell density. The culture was then continued for 4 days at cell density around 100 x 106 cells/mL by performing daily cell bleeds showing that healthy high cell density culture could be obtained somewhat under 130 x 106 cells/mL in the same culture.

Using the TFF, exponential cell growth was obtained at similar rate as with ATF, the cell density was then maintained around 100 x 106 cells/mL by daily cell bleeds for 2 weeks. Then, higher cell densities were achieved, up to more than 200 x 106 cells/mL for 2 days. Reaching 214 x 106 cells/mL coincided with the limit of this system due to high pressure in re-circulation loop (1 bar) related to the viscosity, oxygenation limitation and CO2 accumulation (31 kPa). During these runs, CHO cells were cultivated at high and very high cell densities with a cell viability maintained above 90% (mostly around 95%).

Total mAb production

Over an 17-day period of culture with cell densities maintained at 20-30 x 106 cells/mL, a total of 9 g and 7 g of mAb were harvested in the ATF9 and TFF10 processes respectively (Table 1). The lower yield obtained using the TFF was mainly due to mAb removed in cell bleeds (30% in TFF vs. 19% in ATF). In both cultures, the cell specific production rates of mAb were similar and around 10-15 pg/cell/day (data not shown).

Table 1. Comparison of mAb production using ATF or TFF system at day 17 with cell densities maintained at 20-30 x 106 cells/mL.

Conclusions

A very high cell density of 100 x 106 cells/mL was stably maintained in growing phase and at high viability by performing cell bleeds in a perfused WAVE Bioreactor™ using TFF or ATF cell separations. With the settings used here, the maximal cell density was limited to 214 x 106 cells/mL using TTF and 132 x 106 cells/mL using ATF. Using TFF, the cell density could not be further increased due to the limitations of membrane capacity (for the encountered high viscosity), oxygenation and CO2 level, and using ATF due to pressure limitation to push highly viscous fluid and use of non-pressurisable disposable bioreactor. Thus, the TFF system allowed reaching higher cell densities. To our knowledge, it is the first time that a CHO cell density of more than 200 x 106 cells/mL was achieved in a wave-agitated bioreactor.

Higher retentions of mAb were observed using the TFF system than using the ATF system. In perfusion, the major effect of this retention was loss of mAb in the cell bleeds. Consequently, ATF system was more favourable for production at stable cell density maintained by cell bleeds.

The use of a disposable bioreactor equipped with a disposable separation device offers a solution alleviating technical and sterility challenges occurring in perfusion processes.

Acknowledgements

This work was financed by GE Healthcare. Thank you to Eric Fäldt, Christian Kaisermayer and Craig Robinson from GE Healthcare. We acknowledge The Swedish Governmental Agency for Innovation Systems (VINNOVA), which supported the lab activity. We thank IMED, Sweden, for their kind permission of using their research cell line. We would like also to acknowledge Refine Technology for helpful inputs.