System and method for cell culture scaling
阅读说明:本技术 用于细胞培养缩放的系统和方法 (System and method for cell culture scaling ) 是由 C·布劳 N·琼斯 M·史密斯 于 2019-01-03 设计创作,主要内容包括:本发明实施例集合涉及一种用于产生可缩放生物反应器系统的生物生产系统、方法和装置。具体来说,本发明实施例集合使得能够通过小测试规模的生物反应的操作参数与商业规模的生物反应的操作参数之间的匹配来确定商业规模的生物反应性能特性。所述系统和方法不仅仅依赖于使跨规模的生物反应器装置在尺寸上相同,因为这并没有考虑非常小与非常大的体积之间在流体动力学属性上的差异,而是需要彼此结合来调试各种系统(混合总成、鼓泡器系统和顶部空间气流系统)以实现预期结果。(The present set of embodiments relates to a bioproduction system, method, and apparatus for producing a scalable bioreactor system. In particular, the present set of embodiments enables commercial scale bioreaction performance characteristics to be determined by a match between operating parameters of small test scale bioreactions and operating parameters of commercial scale bioreactions. The systems and methods do not rely solely on making the cross-scale bioreactor apparatus the same in size, as this does not account for differences in hydrodynamic properties between very small and very large volumes, but rather requires the tuning of various systems (mixing assemblies, bubbler systems, and headspace gas flow systems) in conjunction with one another to achieve the desired results.)
1. A scalable bioreactor system for transitioning from testing to commercial production, comprising:
a first bioreactor, comprising:
a first bioprocessing container having a first end, a second end, and a sidewall;
a first configurable mixing assembly suspended between the first end and the second end of the first bioprocessing container; and
a first impeller having a first diameter, the first impeller attached to the first configurable mixing assembly at a first location, wherein the first diameter and the first location are selected to achieve a set of operational parameters;
a second bioreactor comprising
A second bioprocessing container having a first end, a second end, and a sidewall, wherein the second bioprocessing container is a different volume than the first bioprocessing container;
a second configurable mixing assembly suspended between the first end and the second end of the second bioprocessing container; and
a second impeller having a second diameter different from the first diameter, the second impeller attached to the second configurable mixing assembly at a second location, wherein the second diameter and the second location are selected to match the set of operating parameters and the operating parameters include power per volume and impeller tip speed.
2. The scalable bioreactor system of claim 1, wherein the first bioprocessing container comprises a first bubbler attached to the first end of the first bioprocessing container and having a first number of holes and each hole having a first diameter, and the second bioprocessing container comprises a second bubbler attached to the first end of the second bioprocessing container and having a second number of holes and each hole having a second diameter.
3. The scalable bioreactor system of claim 2, wherein the first number of pores is different from the second number of pores, the first diameter is different from the second diameter, and the number of pores and pore size are selected such that the first and second bioreactors achieve the same kLa.
4. The scalable bioreactor system of claim 2, wherein the first and second positions are selected to re-entrain bubbles rising from the first and second bubblers.
5. The scalable bioreactor system of claim 1, wherein the first bioreactor comprises a first headspace gas flow means and the second bioreactor comprises a second headspace gas flow means, and each cross-flow sparger operates to provide a different gas flow rate across the headspace to match the CO2 removal rate of the liquid phase to within five percent between the first bioreactor and the second bioreactor.
6. The scalable bioreactor system of claim 1, wherein the second bioreactor comprises a third impeller having a third diameter different from the first diameter, wherein the third impeller is attached to the second configurable mixing assembly, and the third diameter and third attachment position and the second diameter and the second position are selected to match the set of operating parameters.
7. The scalable bioreactor system of claim 1, wherein a ratio of the first impeller diameter to the first bioprocessing vessel width is different than a ratio of the second impeller diameter to the second bioprocessing vessel width.
8. The scalable bioreactor system of claim 1, wherein the set of operating parameters further comprises total fluid flow and T95 mixing time.
9. The scalable bioreactor system of claim 1, wherein the set of operating parameters is selected based on optimal growth conditions for cells.
10. The scalable bioreactor system of claim 9, wherein the cells are eukaryotic and sensitive to shear forces that increase as the impeller tip speed increases.
11. The scalable bioreactor system of claim 1, wherein the first bioprocessing vessel is a bench-scale volume between 0.1 liters and 50 liters and the second bioprocessing vessel is a commercial volume between 50 liters and 10,000 liters.
12. The scalable bioreactor system of claim 1, wherein the first and second bioprocessing containers are rectangular in shape and the first and second configurable mixing assemblies are offset from a central axis to increase total fluid flow.
13. The scalable bioreactor system of claim 1, wherein the aspect ratio of the first and second bioprocessing containers is greater than 1.5.
14. The scalable bioreactor system of claim 1, wherein the first bioprocessing container has an aspect ratio of between 1.5 and 2 and the second bioprocessing container has an aspect ratio of between 1.75 and 4.
15. A method of matching fluid mixing characteristics between bioreactors having different volumes, comprising:
selecting a first bioreactor having an operational parameter set, the first bioreactor comprising:
a first bioprocessing container having a first end, a second end, and a sidewall; and
a first configurable mixing assembly suspended between the first end and the second end of the first bioprocessing container;
selecting a first impeller having a first diameter;
attaching the first impeller to the configurable mixing assembly, wherein the first diameter and the attachment location are selected to conform to the operating parameters;
selecting a second bioreactor comprising:
a second bioprocessing container having a first end, a second end, and a sidewall, wherein the second bioprocessing container is a different volume than the first bioprocessing container; and
a second configurable mixing assembly suspended between the first end and the second end of the second bioprocessing container;
selecting a second impeller having a second diameter, the second diameter being different from the first diameter;
attaching the second impeller to the second configurable mixing assembly, wherein the second diameter and the second attachment position are selected to match the set of operating parameters, wherein the set of operating parameters includes power per volume and impeller tip speed.
16. The method of claim 15, further comprising the step of: selecting a third impeller having the third diameter different from the first diameter and attaching the third impeller to the second configurable mixing assembly, wherein the third diameter and the third attachment location and the second diameter and the second attachment location are selected to match the set of operational parameters.
17. The method of claim 16, wherein the step of adding the third impeller reduces second and third impeller tip speeds required to maintain power per volume and impeller tip speed in the first and second bioreactors.
18. The method of claim 15, wherein a ratio of the first impeller diameter to the first bioprocessing container width is different than a ratio of the second impeller diameter to the second bioprocessing container width.
19. The method of claim 15, wherein the set of operational parameters further includes total fluid flow and T95 mixing time.
20. The method of claim 19, wherein the set of operational parameters is selected based on optimal growth conditions for the cell.
21. The method of claim 20, wherein the cell is eukaryotic and sensitive to shear forces that increase as the impeller tip speed increases.
22. The method of claim 15, wherein the first bioprocessing container is a bench-scale volume of between 0.1 liters and 50 liters and the second bioprocessing container is a commercial volume of between 50 liters and 10,000 liters.
23. The method of claim 22, wherein the first and second biological treatment vessels are rectangular in shape and the first and second configurable mixing assemblies are offset from a central axis to increase overall fluid flow.
24. The method of claim 23 wherein the first and second bioprocessing containers have an aspect ratio greater than 1.5.
25. A method of matching fluid mixing characteristics between bioreactors having different volumes, comprising:
selecting a first bioreactor having operating parameters, the first bioreactor comprising:
a first bioprocessing container having a first end, a second end, and a sidewall; and
a first configurable mixing assembly suspended between the first end and the second end of the first bioprocessing container;
selecting a first sparger having a first number of holes, wherein the holes have a first diameter, wherein the first number and first diameter are selected to conform to the operating parameters, wherein the first sparger is attached to the first end;
selecting a second bioreactor comprising:
a second bioprocessing container having a first end, a second end, and a sidewall, wherein an aspect ratio of the second bioprocessing container is different from an aspect ratio of the first bioprocessing container; and
a second configurable mixing assembly suspended between the first end and the second end of the second bioprocessing container;
selecting a second bubbler having a second number of holes, wherein the holes have a second diameter, and
the second sparger is attached to the first end of the second biological treatment vessel,
wherein the second number of holes is different from the first number of holes and the second diameter is different from the first diameter, wherein the second number of holes and the second diameter are selected to match the operating parameter to within five percent, wherein the operating parameter is kLa.
26. The method of claim 25, wherein the first bioreactor comprises a first headspace gas flow means and the second bioreactor comprises a second headspace gas flow means, and each headspace gas flow means is operated to provide a different gas flow rate across the headspace to match the operating parameter.
27. The method of claim 25, further comprising the step of attaching a second impeller to the second mixing assembly, wherein the second impeller is configured to re-entrain bubbles rising from the second bubbler, wherein the locations of the bubblers and second impeller and the second number and second aperture are selected to match the operating parameters.
28. The method of claim 25 wherein the aspect ratio of the first bioprocessing container is between 1.5 and 2 and the aspect ratio of the second bioprocessing container is between 1.75 and 4.
29. The method of claim 25, wherein the first bioprocessing container is a bench top volume of between 0.1 liters and 50 liters and the second bioprocessing container is a commercial volume of between 50 liters and 10,000 liters.
30. The method of claim 25, wherein the first and second bioprocessing containers are rectangular in shape and the first and second mixing assemblies are offset from a central axis to achieve a desired kLa.
31. The method of claim 25, wherein kLa refers to O2.
32. The method of claim 25, wherein kLa refers to CO 2.
Background
The biopharmaceutical industry uses a wide range of mixing systems for a variety of processes, such as in the preparation of media and buffers and in the growth, mixing, and suspension of cells and microorganisms. Some conventional mixing systems, including bioreactors and fermentors, include a flexible bag disposed within a rigid support housing. An impeller is disposed within the flexible bag and is coupled with the drive shaft. Rotation of the drive shaft and impeller promotes mixing and/or suspension of the fluid contained within the flexible bag.
Scientists and engineers have focused on creating stirred tank reactors that can not only provide a sterile and well controlled environment for cell culture growth, but also provide robust scale-up solutions from research to manufacturing scale. The traditionally good engineering principles have been applied to design reactors in this way based on linear geometry scaling methods (i.e., vessels will have similar height/diameter ratios and similar impeller/trough diameter ratios). This approach works well in many cases, but the operator must often make many complex decisions as to how best to select the operational settings to obtain repeatable results through scaling up. Since it is a biphasic and metabolism-based system, most of the operating parameters interact dynamically and respond generally non-linearly; optimal parameter selection and process results are often too unpredictable, expensive, and time consuming to properly resolve at the operator level.
Those skilled in the art of biopharmaceutical manufacturing recognize the importance of having good scale-up and scale-down models that are capable of simulating or ideally replicating the physiological growth conditions found in large-scale bioreactors. The reason for the importance of scaling down models is often related to the need for rapid screening of multiple parameters (optimizing cell cloning, culture media, key operating parameters or product quality) and it would be beneficial to be able to perform a wide range of experiments under well controlled conditions at lower cost and with less labor. A good scale-down model will also remove the risk of a desired process in which the likelihood of problems occurring on a large scale will be extremely low, which were not previously identified when occurring on a small scale.
Because larger bioreactors are two-phase systems (gas and liquid based systems), it is difficult to scale down the system in a predictable manner, largely due to solubility differences of the gas types and because the fluidic mechanisms and/or physics of the system are very dynamic (non-linear) due to viscosity, shear forces, density, and surface interactions that are affected across scale. While the overall power dissipation rates using conventional bioreactor designs may be similar, the resulting total flows and measured mixing times are rarely similar on all scales. Thus, problems that are not considered problematic in small scale systems typically occur on a large scale because the same pH, nutrient, gas concentration, or shear gradient found on a large scale cannot be easily replicated in a single operating state produced in a small scale bioreactor.
The main design method currently employed is the geometric scaling of the system (slot height to diameter ratio and impeller to diameter ratio); this operates in conjunction with 1) near constant impeller tip speed or 2) near constant P/V (power input/volume). These methods are quite successful because they allow the operator to compensate for some of the dynamics and non-linearities of mass transfer in rotary agitator-based systems when charging air. However, shear force is conventionally referenced based on the tip velocity of the impeller (where tip velocity is a function of the square of the impeller diameter). Power input/volume is more commonly employed because it is advantageous to meet the practical mechanical design scaling up constraints (meaning that power requirements are within reasonable magnitudes across scale), because power transfer is a non-linear function of speed and diameter (and part of the impeller geometry).
Once the general design of the reactor is known, it is common practice to focus on one of two key process parameters.
Familiar operators often achieve acceptable results with great success if the system is designed correctly, but the overall process is still often plagued by unknown events and time-consuming troubleshooting efforts, especially when it is necessary to facilitate the transfer of the process between different systems as part of a scale-up or to another location.
The problem that is often ignored is the total fluid flow of the system and how it varies across scales. The fluid is displacement and velocity is not linear across scale, so the mixing curve for liquid movement will vary based not only on volume, tip velocity, and diameter. The mixing curve also depends on the spatial distribution of the power within the reactor. In practice, the design should detune the local mixing performance of the smaller volume system to match the overall mixing and mass transfer performance of the large scale system. Since some randomness in mixing or container inversion is beneficial, good design should take into account the effects of obstructions or spoilers in the design.
Disclosure of Invention
In one aspect, a scalable bioreactor system for transitioning from testing to commercial production is disclosed. The system may include: a first bioreactor comprising a first bioprocessing vessel having a first end, a second end, and a sidewall, a first configurable mixing assembly suspended between the first end and the second end of the first bioprocessing vessel, the first impeller having a first diameter, and a first impeller attached to the first configurable mixing assembly at a first location, wherein the first diameter and the first location are selected to achieve a set of operational parameters; and a second bioreactor comprising a second bioprocessing container having a first end, a second end, and a sidewall, and a second configurable mixing assembly suspended between the first end and the second end of the second bioprocessing container, wherein the second bioprocessing container is a different volume than the first bioprocessing container, and a second impeller having a second diameter different from the first diameter, the second impeller attached to the second configurable mixing assembly at a second location, wherein the second diameter and the second location are selected to match a set of operating parameters, and the operating parameters include power per volume and impeller tip speed. In some embodiments, the first bioprocessing container includes a first sparger attached to a first end of the first bioprocessing container and having a first number of holes, and each hole having a first diameter, and the second bioprocessing container includes a second sparger attached to a first end of the second bioprocessing container and having a second number of holes, and each hole having a second diameter. In some embodiments, the first number of wells is different from the second number of wells, the first diameter is different from the second diameter, and the number of wells and the size of wells are selected such that the first and second bioreactors achieve the same kLa. In some embodiments, the first and second positions are selected to re-entrain bubbles rising from the first and second bubblers. In some embodiments, the first bioreactor comprises a first headspace gas flow means and the second bioreactor comprises a second headspace gas flow means, and each cross-flow sparger operates to provide a different gas flow rate across the headspace to match the rate of CO2 removal of the liquid phase to within five percent between the first bioreactor and the second bioreactor. In some embodiments, the second bioreactor comprises a third impeller having a third diameter different from the first diameter, wherein the third impeller is attached to the second configurable mixing assembly, and the third diameter and third attachment location and the second diameter and second location are selected to match the set of operating parameters. In some embodiments, the ratio of the first impeller diameter to the first bioprocessing container width is different than the ratio of the second impeller diameter to the second bioprocessing container width. In some embodiments, the set of operational parameters further includes total fluid flow and T95 mixing time. In some embodiments, the set of operating parameters is selected based on optimal growth conditions for the cell. In some embodiments, the cell is eukaryotic and sensitive to shear forces that increase with increasing impeller tip speed. In some embodiments, the first bioprocessing container is a bench-scale volume between 0.1 liters and 50 liters and the second bioprocessing container is a commercial volume between 50 liters and 10,000 liters. In some embodiments, the first and second biological treatment vessels are rectangular in shape and the first and second configurable mixing assemblies are offset from the central axis to increase overall fluid flow. In some embodiments, the first and second bioprocessing containers have an aspect ratio greater than 1.5. In some embodiments, the first bioprocessing container has an aspect ratio of between 1.5 and 2 and the second bioprocessing container has an aspect ratio of between 1.75 and 4.
In one aspect, a method of matching fluid mixing characteristics between bioreactors having different volumes is disclosed. The method may include selecting a first bioreactor having a set of operating parameters, the first bioreactor comprising: a first bioprocessing container having a first end, a second end, and a sidewall; and a first configurable mixing assembly suspended between the first end and the second end of the first bioprocessing container. The method may include selecting a first impeller having a first diameter and attaching the first impeller to the configurable mixing assembly, wherein the first diameter and attachment location are selected to conform to operating parameters. The method may comprise selecting a second bioreactor comprising: a second bioprocessing container having a first end, a second end, and a sidewall, wherein the second bioprocessing container is a different volume than the first bioprocessing container; and a second configurable mixing assembly suspended between the first end and the second end of the second biological treatment vessel. The method may include selecting a second impeller having a second diameter different from the first diameter, and attaching the second impeller to a second configurable mixing assembly, wherein the second diameter and the second attachment location are selected to match a set of operational parameters, wherein the set of operational parameters includes power per volume and impeller tip speed. The method may include the step of selecting a third impeller having a third diameter different from the first diameter and attaching the third impeller to the second configurable mixing assembly, wherein the third diameter and third attachment location and the second diameter and second attachment location are selected to match the set of operating parameters. In some embodiments, the step of adding a third impeller reduces the second and third impeller tip speeds required to maintain power per volume and impeller tip speed in the first and second bioreactors. In some embodiments, the ratio of the first impeller diameter to the first bioprocessing container width is different than the ratio of the second impeller diameter to the second bioprocessing container width. In some embodiments, the set of operational parameters further includes total fluid flow and T95 mixing time. In some embodiments, the set of operating parameters is selected based on optimal growth conditions for the cell. In some embodiments, the cell is eukaryotic and sensitive to shear forces that increase with increasing impeller tip velocity. In some embodiments, the first bioprocessing container is a bench-scale volume between 0.1 liters and 50 liters and the second bioprocessing container is a commercial volume between 50 liters and 10,000 liters. In some embodiments, the first and second biological treatment vessels are rectangular in shape and the first and second configurable mixing assemblies are offset from the central axis to increase overall fluid flow. In some embodiments, the first and second bioprocessing containers have an aspect ratio greater than 1.5.
In one aspect, a method of matching fluid mixing characteristics between bioreactors having different volumes is disclosed. The method may include selecting a first bioreactor having operating parameters, the first bioreactor including a first bioprocessing vessel having a first end, a second end, and a sidewall; and a first configurable mixing assembly suspended between the first end and the second end of the first bioprocessing container. The method may comprise the step of selecting a first sparger having a first number of holes, wherein the holes have a first diameter, wherein the first number and the first diameter are selected to meet operating parameters, wherein the first sparger is attached to the first end. The method may comprise the step of selecting a second bioreactor comprising: a second bioprocessing container having a first end, a second end, and a sidewall, wherein an aspect ratio of the second bioprocessing container is different from an aspect ratio of the first bioprocessing container; and a second configurable mixing assembly suspended between the first end and the second end of the second biological treatment vessel. The method may comprise the step of selecting a second bubbler having a second number of wells, wherein the wells have a second diameter and attaching the second bubbler to the first end of the second biological treatment vessel, wherein the second number of wells is different from the first number of wells and the second diameter is different from the first diameter, wherein the second number of wells and the second diameter are selected to match an operating parameter to within five percent, wherein the operating parameter is kLa. In some embodiments, the first bioreactor comprises a first headspace gas flow means and the second bioreactor comprises a second headspace gas flow means, and each headspace gas flow means is operative to provide a different gas flow rate across the headspace to match the operating parameter. The method may include the step of attaching a second impeller to the second mixing assembly, wherein the second impeller is configured to re-entrain bubbles rising from the second bubbler, wherein the locations of the bubblers and the second impeller and the second number and second aperture are selected to match the operating parameters. In some embodiments, the first bioprocessing container has an aspect ratio of between 1.5 and 2 and the second bioprocessing container has an aspect ratio of between 1.75 and 4. In some embodiments, the first bioprocessing container is a bench volume between 0.1 liters and 50 liters and the second bioprocessing container is a commercial volume between 50 liters and 10,000 liters. In some embodiments, the first and second bioprocessing containers are rectangular in shape and the first and second mixing assemblies are offset from the central axis to achieve the desired kLa.
Drawings
To readily identify the discussion of any particular element or act, one or more of the most significant digits in a reference number refer to the figure number in which the element is first introduced.
FIG. 1 illustrates a
FIG. 2 illustrates a
Fig. 3 shows a flexible compartment 300 according to an embodiment.
FIG. 4 illustrates a mixing system 400 including a flexible compartment 402 and a spiral assembly 426 according to one embodiment.
FIG. 5 illustrates an exploded view of a
Fig. 6 illustrates a
Fig. 7 illustrates a bubbler 700 design according to one embodiment.
Fig. 8 shows a bubbler 800 according to one embodiment.
FIG. 9 illustrates a
FIG. 10 shows a
FIG. 11 shows a hybrid system 1100 incorporating a gas delivery system according to one embodiment.
Fig. 12 shows a gas delivery system 1200 according to an embodiment.
Fig. 13 shows a
Fig. 14 shows a
Fig. 15 shows a hybrid system 1500 exhibiting a bubble trajectory with a second impeller placed suboptimally.
Fig. 16 shows a
Fig. 17 shows a
Fig. 18A to F show gas distribution patterns using different bubbler locations according to one embodiment.
Fig. 19 shows bubble residence times 1900 from gas generated at various bubbler locations according to one embodiment.
Fig. 20 shows a
Fig. 21 shows
Fig. 22 shows mixing consistency 2200 across a volume scale.
Fig. 23 illustrates a matching
Fig. 24 illustrates a method of matching fluid mixing characteristics between bioreactors having different volumes.
Fig. 25 illustrates a method of matching fluid mixing characteristics between bioreactors having different volumes.
FIG. 26 shows a comparison of Kscore between conventional bioreactors with different volumes.
Fig. 27 shows kLa comparison data across scale.
FIG. 28 shows predicted Kscores between scales in the system described herein.
Detailed Description
Description of the invention
Embodiments of systems, methods, and apparatuses for bioreactor scaling are described in the accompanying description and drawings. In the drawings, numerous specific details are set forth in order to provide a thorough understanding of certain embodiments. The skilled artisan will appreciate that the scalable bioreactor systems and methods described herein can be used for a variety of applications, including, but not limited to, the introduction of cell culture products from laboratory or bench scale into commercial scale production. In addition, the skilled person will understand that certain embodiments may be practiced without these specific details. Moreover, those of skill in the art will readily appreciate that the specific order in which the methods are presented and performed is illustrative and it is contemplated that the order may be varied and still remain within the spirit and scope of certain embodiments.
While the present teachings are described in conjunction with various embodiments, there is no intent to limit the present teachings to such embodiments. On the contrary, the present teachings encompass various alternatives, modifications, and equivalents, as will be appreciated by those of skill in the art.
Moreover, in the various embodiments described, the specification may have presented the method and/or process as a particular sequence of steps. However, to the extent that a method or process does not rely on the particular order of steps set forth herein, the method or process should not be limited to the particular sequence of steps described. Other orders of steps may be possible, as will be appreciated by one of ordinary skill in the art. Therefore, the particular order of the steps set forth in the specification should not be construed as limitations on the claims. Additionally, the claims directed to the method and/or process should not be limited to the performance of their steps in the order written, and one skilled in the art will readily appreciate that the sequences may be varied and still remain within the spirit and scope of the various embodiments.
While preferred embodiments of the present invention have been shown and described herein, it should be obvious to those skilled in the art that such embodiments are provided by way of example only. Those skilled in the art will now recognize numerous variations, changes, and substitutions without departing from the invention. It should be understood that various alternatives to the embodiments of the invention described herein may be employed in practicing the invention. It is intended that the following claims define the scope of the invention and that methods and structures within the scope of these claims and their equivalents be covered thereby.
The invention described herein is a scalable set of bioreactor systems and methods that enable a manufacturer in a bioproduction space to predict the previously discussed physiological growth conditions by altering hardware between scales to achieve similar mixing curves and growth conditions between two or more scales. For example, a scaled bioreactor system may include two or more different sized bioreactors of similar total fluid, similar shear forces at the impeller tips, and similar power input per volume ratios by modifying the geometry of the tank, the size and number of impellers, the ratio of the diameters (widths) of the impellers to the tank, the sparger design, and the CO2 blanket removal system between two or more scales. In other words, two or more bioreactors of the present invention may have distinct physical characteristics while still achieving similar mixing profiles and growth conditions in order to predict commercial scale bioproduction systems at small scale (including bench scale).
The magnitude of the local shear force, the mixed power dissipation ratio and the total fluid flow should be more fully addressed in the scaled-up design. This can be done by optimizing the power distribution of the impellers (increasing the number of impellers in a larger vessel). The overall fluid mixing properties are optimized by limiting how far apart the impellers (increasing in number with increasing volume) are spaced or using CFD or RPT models, and also modifying the size or shape of the impellers (not necessarily shape, but also swept area, blade geometry, surface texture properties or diameter to match the hydrodynamic (vortex) profile created by the fluid movement of the agitator). The main goal is to achieve nearly the same maximum shear level across at least 3 volume-scale values while delivering similar P/V, total flow, T95 mixing time and doing so using reasonable power input values for cell culture and within practical limits imposed by cell culture sensitivity, which may occur in extremely large working volumes (> 1000L). The invention described herein will make the scaling up of the reactor more predictable across scale and therefore easier/logistically debugged because the shear force profiles are similar and the overall fluid movement is nearly the same. The object of the present invention is to solve the now unmet need due to the wide variety of cell culture process sensitivity differences that are inherent in altering cell lines, fluid types, cell densities or media formulations.
The methods herein are designed to achieve the desired result that designing and characterizing reactor scaling-up will be more predictable across scale and therefore easier/logically tuned because the shear force profiles are more similar and the overall fluid movement is nearly the same. The objective here is to address the now unmet need for a wide variety of cell culture process sensitivity differences that are inherently affected when cell lines, fluid types, cell densities or media formulations are altered.
With respect to non-circular containers, it is beneficial to use a rectangular container with a centrally driven agitator that is offset from the centerline for a variety of reasons. An unbalanced design of these two geometries (non-square and non-centered) may produce improved blocking effects and desired mixing inversion (total flow) within the system. Our data supports the idea of improved mass transfer and mixing performance, showing by our performance measurements > 2X improvement in kLa and mixing compared to a circular design at similar working volumes. Scaling the impeller to match tip speed and P/V will produce a proportionally smaller impeller as the vessel's rated working volume decreases. This helps compensate for the inherent changes in fluid mechanics that occur at smaller scales (a proportionally larger impeller-to-vessel wall gap will excite and induce a total flow that is more representative than that of a large scale system). These mixing design features are then combined with optimal sparging locations and this will result in a large increase in bioreactor efficiency at large scale. Two-phase mixing efficiency gains will increase the residence time of the bubbles within the liquid column, and the overall improved bubble distribution from multiple impellers is a highly desirable attribute known to significantly improve mass transfer performance.
Fig. 1 illustrates a
Fig. 2 illustrates a cross-sectional view of a
In various embodiments, a user may open the
In various embodiments, once installation is achieved, fluids may be fed into the sterile
An additional advantage of the yoke/impeller 232 in various embodiments is that it provides extremely low volumetric mixing. For example, the biological reaction may require a smaller volume at the beginning of the reaction, and the fluid volume may increase as the biological reaction is fully completed. Currently available bioreactors have limitations in scaling up, and this example reduces the limitations. One impeller 216 or more may also be attached at various locations on the screw assembly 214 when considering the optimal scaling up of a given bioreactor. In some embodiments, the yoke/impeller 232 can maintain uniform mixing in the fluid at very low volumes during the discharge process.
Fig. 3 illustrates a flexible compartment 300 according to various embodiments. The flexible compartment 300 includes a first end 302; an opposite second end 304; a sidewall 306 connecting the first end 302 and the second end 304; at least three panels 308 joining the first end 302 and the second end 304; a sidewall line 310; a centerline 312; and a corner line 314.
In various embodiments, the centerline 312 is an indicator of a vertical axis running from the center of the first end 302 to the center of the second end 304 of the flexible compartment 300. For example, the centerline 312 may be placed such that the lengths from the centerline 312 to the opposing panel 308 are equal. In various embodiments, the sidewall line 310 may be an indicator of a plane running from the first end 234 to the second end 304 of the flexible compartment 300 and extending from the centerline 312 to a midpoint of the panel 308. In various embodiments, the angle line 314 may be a planar indicator that extends from the first end 302 to the second end 304 of the flexible compartment 300 and extends from the centerline 312 to a position where the two panels 308 are joined to form an angle. In various embodiments, the indicators listed above may be used to determine where the spiral assembly 214 will reside in the flexible compartment 300 when reducing blind zones and increasing overall fluid and thereby improving overall mixing efficiency within the mixing
Fig. 4 illustrates a hybrid system 400 in accordance with various embodiments. The mixing system 400 includes a flexible compartment 402 having a first end 404 and an opposing second end 406 joined together by a sidewall 408 having at least three panels 410 and a sidewall angle 412 where the panels intersect. The flexible compartment 402 may further include one or more inlets 414, one or more outlets 416, one or more bubblers 418, one or more sensor ports 422, optionally containing a sensor 420 and a vent 424. In various embodiments, the screw assembly 426 may be suspended between a first end 434 and a second end 436 of the flexible compartment 402 and have one or more impellers 428 positioned thereon. In various embodiments, the drive shaft 430 may protrude into the first bearing assembly 432 and the first bearing assembly 432 may provide a sterile connection between the drive shaft 430 on the exterior of the flexible compartment 402 to the magnetic yoke on the interior of the flexible compartment 402. In various embodiments, second bearing assembly 440 may be positioned on second end 406 of flexible compartment 402 and may include a pull 444 protruding onto an exterior portion and an opposing/interior portion of flexible compartment 402, second bearing assembly 440 may be connected to yoke/impeller 442. In various embodiments, the spiral assembly 426 may be comprised of a first line 446 and a second line 448 each having a first end 434 connected to the yoke 438 and a second end 436 connected to the yoke/impeller 442, and during operation, may impart rotational movement to mix the fluid 450 within the flexible compartment 402. In various embodiments, the flexible compartment 402 may include an attachment ring 452 attached to or molded as part of the second bearing assembly 222 used, which may slide into a retaining feature on the
In various embodiments, the flexible compartment 402 may include one or more inlets 414 and outlets 416. The inlet 414 may be used during the installation process to add gas into the flexible compartment 402 in order to expand the flexible compartment 402 to its working volume. In addition, inlet 414 may be used to introduce dry media, buffers, liquid nutrients, or anything else that requires mixing. After the mixing process is complete or the bioreaction is achieved to a desired state, the outlet 416 may be used to collect the contents of the flexible compartment 402. Additionally, the vent 424 may be used to empty the flexible compartment 402 of waste. There are various ways known in the art for attaching the inlet 414, outlet 416, and exhaust 424. A common technique is to weld the components to the flexible compartment 402. For example, the components may comprise a polymer that is weldable to the polymer comprising the flexible compartment 402. US 2017-.
In various embodiments, the sensor 422 may be used to monitor environmental conditions within the flexible compartment 402. There are a variety of sensors and sensor ports 420 available on the market, including those described in US 2008-. Various techniques are described in the above-cited references which disclose the manner in which the sensor port 420 is bonded to the flexible compartment 402 using a welding and adhesion method.
In various embodiments, the mixing system 400 described herein can be used to culture cells and then harvest the cells in their entirety or harvest cell byproducts, such as proteins or enzymes. Such biological reactions typically require the introduction of a gas, which is typically accomplished in the bioproduction art using a bubbler 418. Various bubbler 418 designs and methods of attachment thereof are described in US 2013-.
In various embodiments, the first and second bearing assemblies 432, 440 may include first and second annular sealing flanges 454, 456 that may be sealed to the opening on the flexible compartment 402 by welding or bonding around the perimeter. This allows rotational movement of the hub while the housing remains fixed to the flexible compartment 402, allowing the helix assembly 426 to rotate freely within the flexible compartment 402 while remaining sterile to the outside, as disclosed in US 2017-.
In various embodiments, the attachment ring 452 may be engageable to a retaining feature on the
In various embodiments, as depicted in fig. 4, the optimal position of the spiral assembly 426 relative to the flexible compartment 402 will be along the centerline 312.
Fig. 5 is an illustration of an exploded view of a portion of a
In various embodiments, the helical assembly may include one or
In various embodiments, the
In various embodiments, the
In various embodiments,
FIG. 6 is an illustration of one embodiment of a
It should be appreciated that the
As also depicted in fig. 6, the
The
The extruded material may comprise a single unitary sheet comprising two or more layers of different materials each separated by a contact layer. All layers were co-extruded simultaneously. An example of an extrusion material that may be used in the present invention is HyQ CX3-9 film available from HyClone Laboratories, Inc. of Logan, Utah. The HyQ CX3-9 film is a three layer 9mil cast film produced in a cGMP facility. The outer layer is a polyester elastomer coextruded with an ultra low density polyethylene product contact layer. Another example of an extruded material that may be used in the present invention is HyQ CX5-14 cast film also available from HyClone Laboratories, Inc. The HyQ CX5-14 cast film includes an outer polyester elastomer layer, an ultra-low density polyethylene contact layer, and an EVOH barrier layer disposed therebetween. In yet another example, a multi-web film made from three separate blown film webs may be used. The two inner webs were each a 4mil monolayer polyethylene film (HyClone referred to as HyQ BM1 film) while the outer barrier web was a 5.5mil thick 6 layer coextruded film (HyClone referred to as HyQ BX6 film).
The material may be approved for direct contact with living cells and enables the solution to remain sterile. In this embodiment, the material may also be sterilized, such as by ionizing radiation. Examples of materials that may be used in different situations are disclosed in U.S. patent No. 6,083,587, issued on 7/4/2000 and U.S. patent publication No. US 2003/0077466 a1, issued on 24/4/2003, each of which is hereby specifically incorporated by reference.
In one embodiment, the
In still other embodiments, the
It should be appreciated that the
However, in either embodiment, it is generally desirable that when the
Although in the above-discussed embodiments, the
Mounted on the
Although not required, in one embodiment, means for mixing the fluid 630 within the
In yet another alternative embodiment of the means for mixing or mixing assembly, mixing may be achieved by vertically reciprocating a vertical mixer within the
Continuing with fig. 6,
A top view of the
For example, the bubblers 804, 806, 808, 810 are formed by forming weld lines 812, 814, 816, 818 starting at a first location 820 located at or adjacent to the peripheral edge of the first and/or
A plurality of perforations 836 extend through the
In some embodiments, each bubbler may have the same number of perforations 836, and all perforations 836 may be the same size and shape. In an alternative embodiment, the perforations 836 may be different between two or more different bubblers. For example, different bubblers may have different numbers, sizes, and/or shapes of perforations 836 to optimize performance under different conditions. Larger perforations 836 create larger bubbles that may be optimal for stripping C02 from
As discussed in more detail below, the bubblers 804, 806, 808, 810 may be operated simultaneously, or alternatively, a manifold or other regulator may be used so that one or more of the bubblers may be operated without operating the other bubblers. Thus, by having different bubblers with different perforations 836, the selective bubbler may be used at different instances or times to optimize performance.
In some embodiments, it should be appreciated that the gas delivery path 826 of the bubbler 804 is not required. For example, perforations 836 may be formed through the
In one embodiment of the invention, a manifold may be used to control the flow of gas to one or more of the bubblers 804, 806, 808, 810. For example, one embodiment of a manifold 664 incorporating features of the present invention is depicted in FIG. 8. The manifold 664 includes a body 838 having an air inlet 840 and a plurality of air outlets 842, 844, 846, 848. The air outlets 842, 844, 846, 848 communicate in parallel with the air inlet 840 through the forked flow path 850. A gas source (e.g., a compressor or a compressed gas tank) is fluidly coupled to the gas inlet 840. The gas may be air, oxygen, or any other gas or combination of gases. The
Valves 852 are mounted on the body 838 and control the flow of gas to each of the
Fig. 9 illustrates a
In various embodiments,
In various embodiments, the diameter and number of
In various embodiments, the
Fig. 10 illustrates a
In various embodiments, the
Fig. 11 illustrates a hybrid system 1100 incorporating systems and methods for gas stream mass transfer, in accordance with various embodiments. Although gas flow mass transfer is discussed herein primarily with respect to oxygenating a biological culture, the same methods and systems may also be used to oxygenate other types of liquids (such as those mentioned above). Additionally, as discussed in more detail below, the methods and systems of the present invention are not limited to oxygenating a fluid, but may be used with other gases to affect any type of mass transfer into and/or out of a liquid.
Gas stream mass transfer, particularly over conventional sparging techniques, has a number of processing advantages when it is used to oxygenate biological cultures within a reactor vessel. Where the reactor vessel is designed to handle a culture of cells or microorganisms with relatively large changes in fluid volume, the diameter of the vessel generally needs to be relatively large to maintain the geometry and height requirements. As the diameter of the vessel increases relative to the volume, the depth of the culture within the vessel decreases. Thus, for a very small volume of culture in a container, such as when transferring an initial volume of culture into the container, the residence time of the oxygenating bubbles that bubble from the floor of the container into the culture is typically insufficient to properly oxygenate the cultureOxygen. That is, as the depth of the culture is too shallow, the time of the oxygenated bubbles within the culture is insufficient to completely oxygenate the culture as the bubbles travel from the sparger to the top surface of the culture. Likewise for stripping CO2The residence time of the larger bubbling bubbles is also insufficient to completely remove the unwanted CO from the culture2. Due to CO2Gas is heavier than air, so that CO2Like a cover layer, on the top surface of the culture, further hindering oxygenation and CO removal of the culture2Thus, this problem is further exacerbated.
Oxygenation or mass transfer of a gas stream by blowing air or other gas stream containing oxygen over the top surface of the culture becomes more efficient as the depth of the culture or other fluid being treated decreases, as compared to sparging which becomes more efficient as the depth of the culture increases. Thus, gas flow oxygenation is particularly useful for shallow depth cultures disposed within a reactor (including reactors that start at a smaller volume and grow to a larger volume). In addition, bubbling is known to produce unwanted foam on the top surface of the culture, especially when the bubblers used produce extremely small bubbles (sub-millimeter diameter). In contrast, gas stream mass transfer produces minimal foam and can help reduce vessel foam production by reducing the amount of conventional bubbling required. In addition, oxygenation of the gas stream prevents the formation of CO on the surface of the culture2And (4) a covering layer. In this way, the gas on the surface of the culture is both well controlled and thoroughly mixed, thereby enabling CO to be present2Dissipated from the culture, mixed into the headspace of the reactor, and exited via the system vent. The interaction of gas stream oxygenation with system liquid also helps to directly promote stripping of CO from the culture2. Thus, for relatively shallow depth cultures, oxygenation of the gas stream can be used to oxygenate the culture and remove CO from the culture2In some cases, the need for conventional bubbling in some forms of the present invention is eliminated.
Filling the culture at the bottom of the reactor by oxygenation of the gas stream as the depth of the culture in the reactor increasesThe efficiency of oxygen decreases. Thus, as the depth of the culture increases, dissolved O can be used2A sensor or other parameter or mechanism to determine when bubbling or other oxygenation methods should be initiated. That is, as the depth of the culture increases, sparging can be initiated, such as by a stepwise incremental increase or by a continuous gradual increase, in order to ensure that the culture is always properly oxygenated. The applied oxygenation of the gas stream may decrease as sparging increases or may remain constant. Even if the gas stream does not completely oxygenate the culture, the gas stream will still balance the upper region of the culture and prevent CO2This in turn aids in the conventional bubbling operation. Thus, even for relatively deep volumes of culture, gas flow oxygenation can continue to be used in conjunction with bubbling or other oxygenation methods. It should be appreciated that an electronic controller may be used to automatically initiate and/or regulate bubbling and gas flow based on sensor readings.
Examples of systems that may be used to perform gas stream oxygenation/mass transfer will now be discussed. Additional examples of headspace gas flow devices and systems that may be used in the disclosed invention are disclosed in U.S. patent No. 9,388,375 issued on 2016, 7, 12, which is hereby specifically incorporated by reference. One embodiment of a
With continued reference to FIG. 11, the container assembly 16 includes a container 18 having
In the depicted embodiment, container 18 comprises a flexible bag composed of a flexible, water-impermeable material, such as low density polyethylene or other polymeric sheet or film having a thickness in a range between about 0.1mm to about 5mm, with about 0.2mm to about 2mm being more common. Other thicknesses may also be used. The material may consist of a single layer of material, or may comprise two or more layers that are sealed together or separated to form a double-walled container. Where the layers are sealed together, the material may comprise a laminated or extruded material. The laminate comprises two or more separately formed layers which are subsequently secured together by an adhesive. Examples of extrusion materials that may be used in the present invention include HyQ CX3-9 and HyQ CX5-14 films available from HyClonelaboratories, Utah. The material may be approved for direct contact with living cells and enables the solution to remain sterile. In this embodiment, the material may also be sterilized, such as by ionizing radiation. Prior to use, container assembly 16 is typically sealed closed and sterilized such that compartment 28 is sterile prior to introduction of culture 29.
In one embodiment, container 18 may comprise a two-dimensional pillow pouch. In another embodiment, vessel 18 may be formed from a continuous tubular extrudate of polymeric material cut to length. The ends may be sewn closed, or panels may be sealed over the open ends to form a three-dimensional bag. The three-dimensional bag has not only an annular side wall, but also a two-dimensional top end wall and a two-dimensional bottom end wall. Three-dimensional containers may comprise a plurality of discrete panels, typically three or more, and more typically four or six. Each panel is substantially identical and comprises a portion of the side, top and bottom end walls of the container. The corresponding peripheral edges of each panel are sewn together. The gap is typically formed using methods known in the art, such as thermal energy, RF energy, sonic energy, or other sealing energy.
In alternative embodiments, the panels may be formed in a variety of different patterns. Additional disclosure regarding a method of manufacturing a three-dimensional bag is disclosed in U.S. patent publication No. US 2002-0131654a1, published on 9/19/2002, which is specifically incorporated herein by reference in its entirety.
It should be appreciated that the container 18 may be manufactured to have virtually any desired size, shape, and configuration. For example, the container 18 may be formed as a compartment having a size of 10 liters, 30 liters, 100 liters, 250 liters, 500 liters, 750 liters, 1,000 liters, 1,500 liters, 3,000 liters, 5,000 liters, 10,000 liters, or other desired volume. The size of the compartment may also be in a range between any two of the above volumes. Although receptacle 18 may be any shape, in one embodiment receptacle 18 is specifically configured to be substantially complementary to chamber 14 of support housing 12 that receives receptacle 18 such that receptacle 18 is properly supported within chamber 14.
Although in the embodiments discussed above, container 18 is depicted as a flexible bag, in alternative embodiments, it should be appreciated that container 18 may comprise any form of collapsible or semi-rigid container. In still other embodiments, container 18 may be rigid and support housing 12 may be omitted.
Continuing with FIG. 11, formed on container 18 is an example of a plurality of different ports that may be mounted thereon, wherein each port is in communication with a compartment 28. Specifically, mounted on upper end wall 33 are
The bubbling ports 43 and 44 are mounted on the lower end wall 34. A first sparger 52 is mounted to port 43 and is designed to deliver small bubbles of gas to culture 29 to oxygenate culture 29. Bubbler 52 may be integrally formed with or attached to port 43. A second sparger 54 is mounted to port 44 and is designed to deliver larger bubbles to culture 29 for stripping CO from culture 292. As such, the bubbles from the first bubbler 52 are smaller than the bubbles from the second bubbler 54. In some forms of the invention, second bubbler 54 may be an open tube or a tube having a porous frit with relatively large pores, while first bubbler 52 may be a tube having a porous frit with relatively small pores. The first bubbler 52 may further include a perforated or porous film installed on the end of the port 43 or the inner surface of the lower end wall 34 so as to extend over the port 43. It should be appreciated that bubblers are present in a variety of different configurations, and that any type of bubbler may be used as desired or needed for the intended culture volume, cells and conditions.
Note again that container 18 may be formed with any desired number of ports, and the ports may be formed at any desired location on container 18. The ports may be of the same configuration or of different configurations and may serve a variety of different purposes, such as, but not limited to, those listed above. Examples of ports and how various probes, sensors and wires may be coupled to the ports are disclosed in U.S. patent publication nos. 2006-0270036, 2006-11-30 and 2006-0240546, 2006-10-26, which are specifically incorporated herein by reference in their entirety. The ports may also be used to couple the vessel 18 to a secondary vessel, a condenser system, and other desired fittings.
A plurality of vertically spaced
The aseptic connector 72 includes a first connector portion 74 that selectively mates with and fluidly couples a second connector portion 76. A
A
As previously discussed, the goal of the
In one embodiment, gasOxygenation of the fluid stream enables mass transfer of oxygen using only air without the need to resort to bubbling with a kLa factor greater than 3 and more typically greater than 5 or 7. Gas flow oxygenation can also maintain a stable oxygen concentration set point within an active culture, without the need for separate sparging, that is within a range of 30% to 50% of air saturation. The above values can be obtained in stirred tank reactors with mixing by means of impellers and in other types of reactors. In one specific example, gas stream oxygenation using air only was able to oxygenate CHO cultures at a target value of 50% air saturation (868mbar ambient pressure) and to oxygenate CO2Is peeled off to
Cell concentration of 3.5E +06 cells/mL at container volume. At this point, the culture is then fed to the full vessel volume. Notably, at such levels of culture density and vessel fill volume, oxygenation and CO provided by oxygenation of the gas stream2Too high of peeling; it requires the addition of N mixed with air2And CO2To maintain target pH and dissolved O2A target value.During operation, compartment 28 of container 18 is filled with culture 29 such that top surface 31 is positioned adjacent to channel 66. In one embodiment, the distance D between the channel 66 and the top surface 311In the range of between about 0.75cm to about 15cm, with about 1cm to about 10cm or about 2cm to about 5cm being more common. Other distances may also be used. Furthermore, a distance D1May vary based on factors such as the size of the vessel 18, the angle of protrusion of the gas (where flow perpendicular to the liquid surface is optimal), the flow rate of the gas, and the superficial velocity of the gas. When measuring the distance D1When used, the top surface 31 may be the maximum liquid wave height of the culture 29 under agitation, or may be the top surface 31 without agitation. For scalable representation, the flow rate can be measured at the rate of the container volume per minute (VVM) of the maximum rated liquid working volume of the system. The flow rate of gas flowing out through passages 66 is typically in the range of between about 0.06VVM and about 0.2VVM, with about 0.08VVM to about 0.1 VVMVVM or about 0.16VVM to about 0.18VVM is more common. Other flow rates may also be used depending on the intended application. The velocity of the gas exiting the channel 66 or traveling across the top surface 31 within the compartment 28 is typically in a range between about 25 m/sec to about 275 m/sec, with about 25 m/sec to about 175 m/sec or about 30 m/sec to about 100 m/sec being more common. The speed may be greater than 25 m/sec, and more typically greater than 40 m/sec, 60 m/sec, 80 m/sec, or 100 m/sec. To achieve the desired gas velocity exiting passage 66, passage 66 may have a minimum flux exit area in terms of the volume of compartment 12 (i.e., the container volume (VV)). This minimum flux exit area may be about VV (liter)/80 (liter/mm)2) To about VV (liter)/7.8 (liter/mm)2) In a range of between, wherein about VV (liter)/40 (liter/mm)2) To about VV (liter)/30 (liter/mm)2) Or about VV (liter)/8.5 (liter/mm)2) To about VV (liter)/6.25 (liter/mm)2) More commonly. Other areas may be used.
If desired, the
As previously discussed, gas stream oxygenation is most effective for shallow depths of culture 29 within vessel 18. In one embodiment, the maximum distance D between top surface 31 and lower end wall 34 is measured as the diameter of vessel 18 (i.e., the Vessel Diameter (VD))2(see fig. 11) may be over a wide range of distances, and at the maximum distance, the gas stream oxygenation may independently oxygenate the culture 29 to grow cells or microorganisms. For example, the maximum distance D2May range between about vd (cm) 0.3 to about vd (cm) 0.4. In the case where vessel 18 does not have a circular cross-section, VD can be calculated on average diameter. In some embodiments, D depends on the diameter of the container2And may range between about 5cm and 30cm or between 10cm and 100 cm. Other distances may also be used. At some depths, the system mayTo operate without the use of sparging or other oxygenation systems. In addition, for some depths, due to natural circulation caused by the aeration gas, the desired oxygenation can be achieved throughout the culture without the use of a separate mixer. However, as the depth increases, proper oxygenation of the culture requires both gas vapor oxygenation and a separate mixing system (such as thorough impeller or shaking) to ensure that all cultures are properly oxygenated.
As the depth of culture 29 increases,
Gas delivered to container 18 by gas delivery system 60A may be drawn through inlet port 41 so that container 18 does not over-inflate. Due to the relatively large amount of gas passing through vessel 18, the evaporation rate of the medium may be higher relative to conventional systems. As such, the
Culture 29 continues to grow at a level below that of channel 66 until a defined mass density or other desired value is determined in culture 29. Subsequently, valve 86 may be closed and media and other components added to culture 29 until the level of top surface 31 rises to within an operating distance from second gas delivery system 60B shown in fig. 11. Subsequently, gas delivery system 60B is activated to again pass the gas stream over top surface 31, and thereby continue gas stream oxygenation of culture 29. This process may then continue for a subsequent gas delivery system 60C. Likewise, any number of additional gas delivery systems may be vertically spaced along the
Fig. 13 illustrates a
In various embodiments, the
FIG. 14 illustrates a
In various embodiments, the
FIG. 15 illustrates a
In various embodiments, the relative positions of bubbler 1510 and first and second impellers 1506, 1508 are sub-optimal for bubble re-entrainment. There are some applications where a shorter bubble residence time is optimal, but in most cases this is not a desirable configuration.
Fig. 16 illustrates a
In various embodiments, the
Fig. 17 shows a
Fig. 17 sets up an experiment in which a drive shaft (not shown) is offset toward the side walls of the
Fig. 18A to 18F show the bubble distribution pattern of each of the
Fig. 19 shows the performance of
Fig. 20 shows the performance of
Fig. 21 shows comparative data between the volume of a mixing system using the sparging method and system described in the present application and a prior art sparging system. kLa is depicted on the y-axis and flow volume per minute per container volume is depicted on the x-axis. It is clearly demonstrated that the prior art bubbling systems and methods do not produce similar kLa values between 50 liter to 2000 liter systems. However, the bubblers disclosed herein produce very similar values of kLa between systems having different volumes.
Using the methods described above, the aperture and count of the bubbler were scaled, and kLa was measured empirically by comparing the system with FRIT + open tube with the system with FRIT + DHS (bubbler system and method disclosed above).
This approach improves scaling performance across scale, reducing the maximum standard deviation of kLa from 20% to 8.6% across scale, and reducing the average standard deviation of kLa with open tubes or DHS from 16% to 6% across scale.
Fig. 22 shows the mixing uniformity across a volume at a given power input per volume. The
Fig. 23 shows a table demonstrating constant or nearly constant impeller tip speed and power per volume across 50 liter, 100 liter, 250 liter, 500 liter, 1000 liter and 2000 liter systems. The diameter and number of impellers has been varied to accommodate systems of different sizes.
Fig. 24 illustrates a method 2400 of matching fluid mixing characteristics between bioreactors having different volumes, according to various embodiments. Block 2402 includes the step of selecting a first bioreactor having a set of operating parameters, the first bioreactor comprising: a first bioprocessing container having a first end, a second end, and a sidewall; and a first configurable mixing assembly suspended between the first end and the second end of the first bioprocessing container. Block 2404 includes the step of selecting a first impeller having a first diameter. Block 2406 includes the step of attaching the first impeller to the configurable mixing assembly, wherein the first diameter and attachment location are selected to conform to the operating parameters. Block 2408 includes the step of selecting a second bioreactor, the second bioreactor comprising: a second bioprocessing container having a first end, a second end, and a sidewall, wherein the second bioprocessing container is a different volume than the first bioprocessing container; and a second configurable mixing assembly suspended between the first end and the second end of the second biological treatment vessel. Block 2410 includes the step of selecting a second impeller having a second diameter that is different from the first diameter. Block 2412 includes the step of attaching a second impeller to the second configurable mixing assembly, wherein the second diameter and the second attachment position are selected to match a set of operational parameters to within five percent, wherein the set of operational parameters includes power per volume and impeller tip speed.
Fig. 25 illustrates a method 2500 of matching fluid mixing characteristics between bioreactors having different volumes, according to various embodiments. Block 2502 comprises the step of selecting a first bioreactor having operating parameters, the first bioreactor comprising: a first bioprocessing container having a first end, a second end, and a sidewall; and a first configurable mixing assembly suspended between the first end and the second end of the first bioprocessing container. Block 2504 includes the step of selecting a first bubbler having a first number of apertures, wherein the apertures have a first diameter, wherein the first number and the first diameter are selected to comply with operating parameters, wherein the first bubbler is attached to a first end. Block 2506 includes the step of selecting a second bioreactor comprising: a second bioprocessing container having a first end, a second end, and a sidewall, wherein an aspect ratio of the second bioprocessing container is different from an aspect ratio of the first bioprocessing container; and a second configurable mixing assembly suspended between the first end and the second end of the second biological treatment vessel. Block 2508 includes the step of selecting a second bubbler having a second number of wells, wherein the wells have a second diameter and attaching the second bubbler to the first end of the second biological treatment container, wherein the second number of wells is different from the first number of wells and the second diameter is different from the first diameter, wherein the second number of wells and the second diameter are selected to match an operating parameter to within five percent, wherein the operating parameter is kLa.
A series of predicted and actual data were collected and presented in figures 26, 27 and 28. The following is a way to predict the required pore size to ensure scaling across bioreactors with different volumes.
1. Using regression based on empirical data and literature, the following are predicted:
a. bubble size from pore size and flow rate (regression of internal empirical data)
b. Bubble terminal velocity (talaria, 2007, the terminal velocity of bubble rise in the liquid column, also verified by measuring the velocity of bubbles in the chamber).
c. Residence time based on liquid column height divided by bubble terminal velocity
kLa score is based on:
FIG. 26 shows the cross-scale predictive Kscore comparison data on a conventional bioreactor.
Fig. 27 shows actual kLa comparison data across scale on a conventional bioreactor.
FIG. 28 shows predicted Kscore comparison data across scales on some embodiments disclosed herein.
Using the systems and methods disclosed herein, operating parameters can be kept constant across mixing systems that accommodate different volumes. When moving from a test or bench scale to a commercial scale, the most important aspect is the ability to easily predict the growth conditions of the bioreactor. The scalable system herein allows a user to create such a system by adjusting various aspects of the bubbler design, drive system, and headspace gas flow system, where the components across the system may be completely different, but produce the same or similar results. It should be noted that all systems interact with each other and other aspects need to be considered when making a selection. For example, if increased bubble residence time is desired, the drive system can be altered to re-entrain the bubbles. Additional sparging and gas flow across the headspace may be added if needed to reduce CO2 build-up. To date, users need to determine more important metrics (shear force, power per volume, or kLa) and design scalable systems (vessel aspect ratio, impeller diameter, vessel width/diameter, etc.) that are the same in size. With the disclosed invention, various operating parameters can be kept constant with an understanding of how the various systems affect each other.
While the present teachings are described in conjunction with various embodiments, there is no intent to limit the present teachings to such embodiments. On the contrary, the present teachings encompass various alternatives, modifications, and equivalents, as will be appreciated by those of skill in the art.
Further, in describing various embodiments, the specification may have presented the method and/or process as a particular sequence of steps. However, to the extent that a method or process does not rely on the particular order of steps set forth herein, the method or process should not be limited to the particular sequence of steps described. Other orders of steps may be possible, as will be appreciated by one of ordinary skill in the art. Therefore, the particular order of the steps set forth in the specification should not be construed as limitations on the claims. Additionally, the claims directed to the method and/or process should not be limited to the performance of their steps in the order written, and one skilled in the art will readily appreciate that the sequences may be varied and still remain within the spirit and scope of the various embodiments.
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