In general terms, bioreactors are devices in which biological and/or biochemical processes develop under tightly controlled environmental and operating conditions that are closely monitored. These conditions include temperature, pH, nutrient supply, pressure, and waste removal. A bioreactor may also refer to a device or system intended to grow cells or tissues in the context of cell culture. Such devices are being developed for use in tissue engineering. The bioreactors are also beneficial because they allow specific experimental bioprocesses, along with control and the ability to reproduce at high level. This automated system has become vital for their transfer to large-scale applications.
Bioreactor technologies produced for the purpose of tissue engineering can be used to grow functional cells and tissues for transplantation. Such technologies can also be used for controlled in vitro studies based on the regulation effect of biochemical and biomechanical factors on cell and tissue development. The principal objectives of these systems are to create spatially uniform cell distributions on three dimensional scaffolds, to sustain desired concentrations of gases and nutrients in the culture medium, and to expose the developing tissue to appropriate physical stimuli.
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A range of different bioreactors have been developed and used in order to grow cells and tissues. The different types include spinner flask, rotating wall vessel, hollow-fiber and direct perfusion bioreactors. Spinner flask bioreactors have been used for the seeding of cells into 3D scaffolds and for subsequent culture of the constructs (Vunjak-Novakovic et al., 2002). The process of seeding involves cells being transported to and into the scaffold via convection. During culture, medium stirring increases external mass-transfer but also generates turbulent eddies, which could be harmful for the development of the tissue.
Rotating-wall vessels provide a dynamic culture environment to the constructs, with high mass-transfer rates and low shear stresses. The walls of the vessel are rotated in such a way that enables the drag force (Fd), centrifugal force (Fc) and net gravitational force (Fg) on the construct to be balanced, this allows the construct to remain in a state of free-fall through the culture medium (Unsworth and Lelkes, 1998).
During the culture of highly metabolic and sensitive cell types such as hepatocytes, mass transfer can be improved by the use of Hollow-fiber bioreactors. In one configuration, cells are embedded inside a gel within the lumen of permeable hollow fibers and medium is perfused over the external surface of the fibers (Jasmund and Bader, 2002).
Direct perfusion bioreactors have been proven to enhance: growth, differentiation and mineralized matrix deposition by bone cells (Bancroft et al., 2002, Goldstein et al., 2001), proliferation of human oral keratinocytes (Carrier et al., 2002), albumin synthesis rates by hepatocytes (Kim et al., 2000), expression of cardiac-specific markers by cardiomyocytes (Carrier et al., 2002) and GAG synthesis and accumulation by chondrocytes (Pazzano et al., 2000). Thus when integrated into a bioreactor design, direct perfusion can be used as a valuable tool for prolonging cell survival, growth and function. However, the effects of direct perfusion can be highly dependent on the medium flow-rate and the maturation stage of the constructs, as recently demonstrated for 3D cultures of chondrocytes (Davisson et al., 2002). Therefore, it is vital that a perfusion bioreactor built for the engineering of a 3D tissue must ensure a careful balance between the mass transfer of nutrients and waste products to and from cells, the preservation of newly synthesized extracellular matrix components within the construct, and the shear stresses induced by fluid within the scaffold pores.
The first major step in establishing a 3D culture involves high density cell seeding and uniform distribution of cells on scaffolds, and may also play a crucial role in influencing the progression of tissue formation (Vunjak-Novakovic et al., 1998). Seeding cells into scaffolds at high densities has been related with enhanced tissue formation in 3D constructs, including higher rates of production of cartilage matrix (Freed et al., 1997), increased bone mineralization (Holy et al., 2000), and an enhanced structure of cardiac tissue (Carrier et al., 1999).
The preliminary distribution of cells within the scaffold following seeding has been linked to the distribution of tissue subsequently formed within engineered constructs (Freed et al., 1998). This suggests that uniform cell-seeding could establish the basis for uniform tissue generation. However, it can be a significant challenge to distribute a high density of cells efficiently and uniformly throughout the scaffold volume even with a small 3D scaffold.
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Static loading of cells onto a scaffold is by far the most frequently used method of seeding, but several studies have reported low seeding efficiencies (Holy et al., 2000) and non-uniform cell distributions within scaffolds (Kim et al., 1998), due partly to the manual and operative nature of the process. Studies show that stirred-flask bioreactors produce significantly higher efficiencies and uniformities when poly glycolic acid non-woven meshes were seeded onto a scaffold (Bursac et al., 1996). Perfusion seeding has been reported to be a more effective method to improve both seeding efficiency and cell distribution in comparison to static seeding or the stirring-flasks bioreactor. Perfusion seeding bioreactors have been designed for engineering vascular grafts, cartilage, hepatocyte and cardiac tissues (Wendt et al., 2003).
The fact that the supply of oxygen and soluble nutrients becomes critically limiting for the in vitro culture of 3D tissues has long been known. The result of such a limitation is proven by early studies showing that cellular spheroids greater than 1 mm in diameter generally contain a hypoxic, necrotic center, surrounded by a rim of viable cells (Sutherland et al., 1986). Mass transfer limitations represent one of the greatest challenges to be addressed due to tissue engineered constructs required be at least a few mm in size.
The rotating wall bioreactor can improve nutrients and wastes transfer and provide low stress by generating a dynamic flow. Research findings have shown that properties of engineered tissue cultured in the rotating wall bioreactor were greater to those of static or stirring-flask bioreactor. The efficacy of rotating wall vessel (RWV) bioreactors for the generation of tissue equivalents has been demonstrated using chondrocytes (Vunjak-Novakovic et al., 1999), cardiac cells (Carrier et al., 1999) and various tumor cells (Rhee et al., 2001). Following a few weeks of cultivation in the RWVs, cartilaginous constructs had biochemical and biomechanical properties superior to those of static or stirred-flask cultures and similar to those of native cartilage (Vunjak-Novakovic et al., 1999). Based on these studies, it was proposed that the RWV bioreactor would support the engineering of tissues and organoids as in vitro model systems of tissue development and function (Unsworth and Lelkes, 1998)
Bioreactors used to perfuse medium either through or around semi-permeable hollow fibers have successfully been used to maintain the function of highly metabolic cells (e.g. hepatocytes) by increasing the mass transport of nutrients and oxygen (Jasmund and Bader, 2002). This concept has been extended to engineered tissues via perfusion of culture medium directly through the pores of the cell-seeded 3D scaffold, thus in turn reducing mass transfer limitations both at the construct periphery and within its internal pores (Wendt et al., 2003).
Increasing evidence suggests that mechanical forces, which are known to be significant modulators of cell physiology, may increase the biosynthetic activity of cells in bioartificial matrices and, therefore, possibly improve or accelerate tissue regeneration in vitro (Butler et al., 2000). Studies conducted on musculoskeletal tissue engineering have demonstrated the validity of this principle. For example, cyclical mechanical stretch was found to: enhance proliferation and matrix organization by human heart cells seeded on gelatin-matrix scaffolds (Akhyari et al., 2002), improve the mechanical properties of tissues generated by skeletal muscle cells suspended in collagen or Matrigel (Powell et al., 2002) and increase tissue organization and expression of elastin by smooth muscle cells seeded in polymeric scaffolds (Kim et al., 1999).
Although numerous proof-of-principle studies have shown that mechanical conditioning can improve the structural and functional properties of engineered tissues, little is known about the specific mechanical forces or regimes of application (i.e. magnitude, frequency, continuous or intermittent, duty cycle) that are stimulatory for a particular tissue. Also, engineered tissues at different stages of development might require different regimes of mechanical conditioning due to the increasing accumulation of extracellular matrix and developing structural organization.
The role of bioreactors in applying mechanical forces to 3D constructs could be expanded beyond the conventional approach of enhancing cell differentiation and/or extracellular matrix deposition in engineered tissues. For example, they could also serve as valuable in vitro models to study the physiological effects of physical forces on developing tissues. They may also be used to predict the responses of an engineered tissue to physiological forces on surgical implantation. Together with biomechanical characterization, bioreactors could consequently help in defining when engineered tissues have a sufficient mechanical integrity and biological responsiveness to be implanted (Demarteau et al., 2003). Furthermore, quantitative analysis and computational modelling of stresses and strains experienced both by normal tissues in vivo for a variety of activities and by engineered tissues in bioreactors, could lead to more specific comparisons of in vivo and in vitro mechanical conditioning, and in turn help to determine potential regimes of physical rehabilitation that are most appropriate for the patient receiving the tissue (Butler et al., 2000).
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By providing a comprehensive level of monitoring and control over specific environmental factors in 3D cultures, bioreactors can provide the technological means to carry out controlled studies aimed at understanding which specific biological, chemical or physical parameter plays what role in engineering a defined tissue. At this point, the transition from laboratory- to industrial-scale will require a switch from highly flexible bioreactors to specialized bioreactors, putting into practice the defined bioprocesses in a standardized way. In the future we will see a tremendous amount of development in bioreactors in which the resulting devices will provide an economically viable means to the automated manufacture of functional grafts, perhaps bringing cell-based tissue engineering approaches to become clinically accessible at a larger scale.
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