Patent Application
20230183634
The present disclosure relates generally to the field of biotechnology and flow rate optimizing. In particular, the present disclosure relates to a cell culture apparatus, methods for cell cultivation by using the cell culture apparatus, and a cell culture incubator comprising the cell culture apparatus.
Cell culture or cell cultivation involves growing cells of desired type(s) outside a living body under controlled in vitro conditions to sustain cell growth and viability. The cell culture is widely used in different biotechnology branches, including cell biology, tissue engineering, biomedical engineering, cell differentiation studies, cell-based biosensors, cell-cell interaction, cell-signaling, cell-migration, physiological and pathophysiological studies, etc.
Environmental conditions created for cultured cells should resemble as closely as possible the conditions experienced by the same cells in vivo. This may be done by performing the cell culture in large vessels, such as dishes, spinner and shaker flasks, etc. However, the cell culture conditions provided by these vessels do not truly represent the in vivo environment of the cells being cultured. Moreover, since these vessels have a large volume, they consume significant amounts of reagents, culture media, chemicals, etc., thereby making it difficult to control and/or alter the cell culture conditions.
With the advent of microfluidics, new devices and methods configured to cultivate various types of cells, like adherent and non-adherent, under uniform and controlled in vitro conditions have been developed. Unlike the conventional cell culture methods based on the above-mentioned vessels, microfluidic cell culture methods may provide continuous nutrient (culture fluid or medium) supply, waste removal, flexibility of schedules, and high automation capability. The less consumption of fluids, their low volumes and therefore the reduced time and cost of cell cultivation make these microfluidic methods particularly interesting for cell-based assays. The main goals of microfluidic cell culture devices are to mimic closely in vivo cellular microenvironments and to maintain simplicity for reproducible results.
However, the limiting factors of the current microfluidic cell culture devices are their low throughput and incompatibility with available liquid handling systems and imaging systems due to the discrete arrangement and limited number of microfluidic channels. Furthermore, fluid flow control in the current microfluidic cell culture devices is often limited to one method and not flexible enough to adapt to different resource settings and different cell-based assays.
This summary is provided to introduce a selection of concepts in a simplified form that are further described below in the detailed description. This summary is not intended to identify key features of the present disclosure, nor is it intended to be used to limit the scope of the present disclosure.
It is an objective of the present disclosure to provide a technical solution, wherein in each culture medium reservoir, flow outlets may be compatible with existing robotic liquid handling systems. In particular, the flow outlets may have a conical shape to provide an optimized cell loading and flow mechanism and to guide the cells to attach to the membrane area. Too high injection rate may damage the cells and too low injection rate may make the cell settle along the flow path.
The objective above is achieved by the features of the independent claims in the appended claims. Further embodiments and examples are apparent from the dependent claims, the detailed description and the accompanying drawings.
According to a first aspect, a cell culture apparatus is provided. The apparatus may comprise a plurality of cell culture modules arranged adjacent to each other. Each cell culture module of the plurality of cell culture modules may comprise at least two culture medium reservoirs, a first chamber, a second chamber, a membrane, at least two flow channels, and a cavity. Each of the at least two culture medium reservoirs may have a top part and a bottom part, with the top part having an inlet for a culture medium and the bottom part having an outlet for the culture medium. The first chamber may be arranged between the at least two culture medium reservoirs such that the first chamber and the at least two culture medium reservoirs may be aligned with each other in a first direction. The second chamber may be arranged under the first chamber and aligned with the first chamber in a second direction. The second direction may be perpendicular to the first direction. The second chamber may have a bottom part having at least two lateral holes. The bottom part of the second chamber may be arranged higher than the bottom part of each of the at least two culture medium reservoirs. The membrane may have through pores formed therein and may be arranged between the first chamber and the second chamber such that the first chamber and the second chamber are in flow communication with each other via the through pores. Each of the at least two flow channels may connect the outlet of the bottom part of one of the at least two culture medium reservoirs to one of the at least two lateral holes of the bottom part of the second chamber. The apparatus may further comprise a flow driving unit configured to cause the culture medium to flow, in each cell culture module of the plurality of cell culture modules, between the at least two culture medium reservoirs via the at least two flow channels and the second chamber. Also, the bottom part of the at least two culture medium reservoirs may comprise a holding member. The bottom part of the at least two culture medium reservoirs may comprise a holding member configured to be compatible with a liquid handling system. The bottom part of the at least two culture medium reservoirs may comprise a holding member for a liquid handling system. With this configuration, the cell culture apparatus may cultivate cells of the same or different types on the basal (i.e., bottom) surface of the porous membranes in the cell culture modules under uniform and controlled in vitro conditions. Moreover, the deposition of the cells on the basal surface of the porous membranes may be provided without having to invert the apparatus or to use high concentrations of the cells in the culture medium to cause the cells to bond and cover the membrane. It may also be possible to provide optimized cell loading and flow mechanism and to guide the cells to attach to the membrane area.
According to an example embodiment of the first aspect, the holding member may have a truncated cone shape. This kind of shape may allow the liquid handling system to be placed at least partly firmly inside the flow outlet. This culture medium may flow directly from the liquid handling system, for example from a tip of the pipetting device, through the flow outlet straight to the flow channel. This may allow direct control of the culture medium loading to the flow channels with the liquid handling system.
According to an example embodiment of the first aspect, the bottom of the culture medium reservoir may continue as the holding member, and a top edge of the holding member may comprise the outlet for the culture medium.
According to an example embodiment of the first aspect, the bottom of the culture medium reservoir may continue as the holding member, and a top edge of the holding member may comprise the outlet for the culture medium, wherein the outlet for the culture medium may be configured to receive at least part of the liquid handling system. This kind of shape may let the culture medium to flow directly from the liquid handling system, for example from the tip of the pipetting device, through the flow outlet straight to the flow channel. This may allow direct control of the culture medium loading to the flow channels.
According to an example embodiment of the first aspect, the holding member may have a bottom edge at the bottom of the culture medium reservoir, wherein the bottom edge of the holding member may have a larger diameter, and the top edge of the holding member may have a smaller diameter. The holding member may be located inside the culture medium reservoir. Height of the holding member may also increase from the bottom part of the culture medium reservoir towards the top part of the culture medium reservoir. The bottom edge of the holding member may be located at the center of the bottom part of the culture medium reservoir. All these features may facilitate placing at least part of the liquid handling system inside the flow outlet.
According to an example embodiment of the first aspect, a side of the holding member may extend at a second tilting angle to the first direction starting at the bottom of the corresponding culture medium reservoir. With such titled sides, it may be possible to improve holding of the liquid handling system at least partly inside the flow outlet.
According to an example embodiment of the first aspect, the outlet for the culture medium may be configured to receive at least part of the liquid handling system and the culture medium may be configured to be directed through the outlet to the flow channel. The flow channel may start seamlessly straight from the bottom edge of the holding member. This may allow direct control of the culture medium loading to the flow channels.
According to an example embodiment of the first aspect, the at least one culture medium reservoir may comprise an overflow cavity between the holding member and the bottom of the culture medium reservoir. The overflow cavity may be located between an outer part of the holding member and an inner part of the bottom of the culture medium reservoir. The conical inlet/outlet design of the holding member may create the overflow cavity on the bottom part of the culture medium reservoirs to store excess liquid, thus may prevent the culture medium reservoirs to dry out.
According to an example embodiment of the first aspect, the culture medium is configured to be injected through the outlet to the flow channel, wherein an injection rate for the culture medium from the outlet of the culture medium to the flow channel may be smaller than a maximum viable cell flow rate and larger than a cell settling rate, wherein the injection rate is the speed of cell suspensions being injected into the flow channel; the maximum viable cell flow rate is the maximum speed of the cell suspension or culture medium flows at which the cells will be damaged or dead if exceeded; and cell settling rate is a speed at which the cells in the culture medium will settle to the bottom of the chamber, reservoir, flow channel, and/or culture medium. The optimized injection rate may provide an optimized cell loading and flow mechanism and guide the cells to attach to the membrane area. Too high injection rate may damage the cells, too low injection rate may make the cell settle along the flow channel or the chamber.
According to an example embodiment of the first aspect, an optimal injection time may be configured to be calculated by dividing amount of the culture medium by the injection rate. This may allow to calculate optimal injection time by using the optimal injection rate. The liquid handling system may be used to optimize the injection rate and/or the injection time.
According to an example embodiment of the first aspect, at least part of at least one of the following may be coated, from inside, with a cell repellent layer: at least one flow channel, at least one culture medium reservoir, first and/or second chamber in at least one cell culture module of the plurality of cell culture modules. The cell repellent coating or layer may be used for forming organoid on top of the membrane and preventing the cells to adhere to some specific parts of the microchannels or flow channels. In some example embodiments, only the membrane areas may be used for cell adherence, which may reduce the number of cells needed and avoid non-specific binding. According to an example embodiment, top and/or bottom surface of the membrane may be coated with a cell adhesion enhancing coating.
According to an example embodiment of the first aspect, the cell repellent layer may be made of at least one of the following material: Teflon, Pluronic, PEG, or similar chained polymers. The cell repellent layer may be used to prevent the cells to adhere to some specific parts of the apparatus.
According to an example embodiment of the first aspect, each cell culture module of the plurality of cell culture modules may comprise a cavity at least under the bottom part of the second chamber. The cavity may allow deposition of the cells on the basal surface of the porous membranes without having to invert the apparatus or to use high concentrations of the cells in the culture medium to cause the cells to bond and cover the membrane.
According to an example embodiment of the first aspect, each of the at least two flow channels may extend at least partly at a tilting angle to the first direction and the bottom part of the second chamber and at least part of each of the at least two flow channels form the cavity. A bent or slope structure on the second chamber or the at least one of the flow channels may facilitate cell deposition on the bottom surface of the membrane without having to invert the whole cell culture module.
According to an example embodiment of the first aspect, each of the at least two flow channels in at least one cell culture module of the plurality of cell culture modules may comprise a first channel portion and a second channel portion. The first channel portion may extend from the bottom part of one of the corresponding culture medium reservoirs and be parallel to the first direction. The second channel portion may connect the first channel portion to the one of the at least two lateral holes of the second chamber. The second channel portion may extend at least partly at the tilting angle to the first direction. The bottom part of the second chamber and at least part of each second channel portions of the at least two flow channels may form the cavity. With this configuration of the flow channels, it is possible to improve flow characteristics in each cell culture module, thereby improving the cell delivery to the second chamber.
According to an example embodiment of the first aspect, each of the at least two flow channels in at least one cell culture module may extend at a tilting angle to the first direction starting from the bottom part of the corresponding culture medium reservoir. The bottom part of the second chamber and at least part of the each of the at least two flow channels may form a cavity. This means that there may be no first channel portion parallel to the first direction. With such configuration, the flow channels may be easier and cheaper to manufacture.
According to an example embodiment of the first aspect, the tilting angle may fall within a range of 5 degrees to 45 degrees. With such titled flow channels, it may be possible to achieve appropriate flow characteristics and, therefore, improve cell delivery to the second chamber.
According to an example embodiment of the first aspect, each of the at least two flow channels in at least one cell culture module of the plurality of cell culture modules may have a variable or constant channel height; and/or a variable channel width which may increase towards the second chamber. With this configuration of the flow channels, it may be possible to improve flow characteristics in each cell culture module, thereby improving the cell delivery to the second chamber and, consequently, the cell attachment to the basal surface of the porous membrane.
According to an example embodiment of the first aspect, the variable channel width gradually increases towards the second chamber. This may allow achieving better retainment of the laminar flow of the culture medium in the flow channels.
According to an example embodiment of the first aspect, the first chamber in at least one cell culture module of the plurality of cell culture modules may be implemented as a bottomless hollow tube. With this first chamber, it may be possible to deposit cells on the apical (i.e., top) surface of the porous membrane. The cells deposited on the apical surface of the porous membrane may be of the same or other type compared to the cells deposited on the basal surface of the porous membrane. Thus, the first chamber thus configured may allow one to deposit a cell monolayer on the apical surface of the porous membrane and study the interaction of the cells deposited on the basal and apical surfaces of the membranes. Moreover, with such configuration, the first chamber is easier and cheaper to manufacture.
According to an example embodiment of the first aspect, the first chamber in at least one cell culture module of the plurality of cell culture modules may be implemented as a hollow tube having a curved or angled bottom. In this embodiment, the curved or angled bottom may have at least one cavity and at least one hole formed in each of the at least one cavity. With this first chamber, it may be possible to deposit cells on separate portions of the apical surface of the porous membrane. This configuration of the first chamber may be especially useful for forming similar or different particles under study (e.g., organoids or spheroids) on the apical surface of the porous membrane and study their interaction with the cells deposited on the basal surface of the porous membrane.
According to an example embodiment of the first aspect, the curved or angled bottom may be coated, from outside, with a cell adhesion enhancing layer such that the at least one hole of the at least one cavity may remain open. The cell adhesion enhancing layer may be made of a hydrophilic material (e.g., type I collagen). With such a coating layer, the cells may clump outside the bottom of the first chamber and further adhere onto the apical surface of the porous membrane. Thus, this coating layer allows for less cells to be used in an experiment and more precise deposition of the cells on the apical surface of the porous membrane. In turn, the smaller number of cells also may mean less cell death or, in other words, more healthy cells in the cell culture as dead cells may tend to release factors promoting apoptosis.
According to an example embodiment of the first aspect, the second chamber may have a height falling within a range from 50 μm to 150 μm. By using such a second chamber, it is possible to make the cell culture apparatus according to the first aspect more compact.
According to an example embodiment of the first aspect, the second chamber in at least one cell culture module of the plurality of cell culture modules may be coated, from inside, with a cell adhesion enhancing layer. The cell adhesion enhancing layer may be made of a hydrophilic material. (e.g., type I collagen). With such a coating layer, the cells may attach onto the basal surface of the porous membrane more efficiently. Thus, this coating layer may allow for less cells to be used in an experiment and more precise deposition of the cells on the basal surface of the porous membrane. In turn, the smaller number of cells also may mean less cell death or, in other words, more healthy cells in the cell culture as dead cells may tend to release factors promoting apoptosis.
According to an example embodiment of the first aspect, each of the at least two flow channels in at least one cell culture module of the plurality of cell culture modules may be coated, from inside, with a cell adhesion enhancing layer. The cell adhesion enhancing layer may be made of a hydrophilic material (e.g., type I collagen). By using the adhesion enhancing layer, cell attachment onto the sides of the flow channels (as well as on the sides of the second chamber and the porous membrane) may become stronger, cell proliferation may be appropriate to a tissue being modelled, and cell viability may be better. Selecting the correct adhesion enhancing layer may also play a role in the proper communication between cell types. Thus, this coating layer may allow for less cells to be used in an experiment and more precise deposition of the cells on the basal surface of the porous membrane. In turn, the smaller number of cells may also mean less cell death or, in other words, more healthy cells in the cell culture as dead cells may tend to release factors promoting apoptosis.
According to an example embodiment of the first aspect, the flow driving unit may be configured to cause the culture medium to flow, in each cell culture module of the plurality of cell culture modules, between the at least two culture medium reservoirs by:
Thus, unlike the current microfluidic cell culture devices, the cell culture apparatus according to the first aspect may be compatible with different flow control means, i.e., pneumatic pump-actuated flow control, and pumpless flow control (which is provided by means of gravity as a result of rocking the plurality of cell culture modules or by means of culture medium pipetting).
According to an example embodiment of the first aspect, each of the at least two culture medium reservoirs in at least one cell culture module of the plurality of cell culture modules may be implemented as a hollow tube. With such configuration, the culture medium reservoirs may be easier and cheaper to manufacture.
According to an example embodiment of the first aspect, the bottom part of each of the at least two culture medium reservoirs may have a positively tapered profile. By using such a configuration of the culture medium reservoirs, it may be possible to cause the whole culture medium contained in the culture medium reservoirs to flow to the bottom towards the second chamber even when the apparatus is tilted, so that no culture medium may be left in the culture medium reservoirs. This also may help to reduce the number of cells that may be needed to be deposited or grown on the basal surface of the porous membrane. Additionally, this configuration of the culture medium reservoirs may allow one to achieve optimal flow rates in each cell culture module.
According to an example embodiment of the first aspect, at least one cell culture module of the plurality of cell culture modules further may comprise a first electrode arranged in the first chamber and a second electrode arranged in the second chamber. These electrodes may serve different purposes. For example, they may be used to feed electrical pulses to muscle or nerve cells present in the first and second chambers or be coupled to other sensors of various types. More specifically, these electrodes may be used to perform real-time Transepithelial/Transendothelial Electrical Resistance (TEER) measurements; in this case, signals may be read out by an external control unit.
According to an example embodiment of the first aspect, at least one cell culture module of the plurality of cell culture modules may further comprise a first electrode arranged in one or more of the at least two culture medium reservoirs and a second electrode arranged in the first chamber. This arrangement of the first and second electrodes may be also used to perform the TEER measurements, for example.
According to an example embodiment of the first aspect, at least one cell culture module of the plurality of cell culture modules may further comprise at least two third electrodes arranged in the first chamber. The third electrodes may be arranged on the same wall or on opposite walls inside the first chamber. These electrodes may be used to perform liquid/medium level measurements in the first chamber.
According to an example embodiment of the first aspect, at least one cell culture module of the plurality of cell culture modules may further comprise at least two fourth electrodes imbedded into the membrane. These electrodes may be used, for example, to provide different stimulus signals to the cells deposited on the apical and/or basal surface of the membrane.
According to an example embodiment of the first aspect, at least one cell culture module of the plurality of cell culture modules may further comprise at least one of the following: an oxygen sensor, a pH sensor, and/or a CO2 sensor in the first chamber and/or the second chamber. These sensors may enable real-time measurements of parameters crucial for cell behavior.
According to an example embodiment of the first aspect, the through pores of the membrane may have an average pore size falling within a range from 0.2 μm to 10 μm. By varying the average pore size within this range, it may be possible to study the behavior of cells of different sizes, which may be deposited on one or each of the apical and basal surfaces of the membrane.
According to a second aspect, a cell culture incubator is provided. The cell culture incubator may comprise the cell culture apparatus according to the first aspect, and a liquid handling system configured to feed the culture medium to at least one of the at least two culture medium reservoirs and/or to at least one outlet of the at least two culture medium reservoirs in each cell culture module of the plurality of cell culture modules. The liquid handling system may be a robotic liquid handling system, for example a pipetting station. The liquid handling system may be used to optimize the injection rate and/or the injection time. With this configuration, the cell culture incubator may cultivate cells of the same or different types on the porous membranes of the cell culture modules under unform and controlled in vitro conditions. Moreover, the deposition of the cells on the basal surface of the porous membranes may be provided without having to invert the cell culture apparatus or to use high concentrations of the cells in the culture medium to cause the cells to bond and cover the membrane.
According to an example embodiment of the second aspect, operation (a) may comprise controlling feeding of the culture medium from the outlet of the culture medium to the flow channel by optimizing injection rate, wherein optimal injection rate for the culture medium from the outlet of the culture medium to the flow channel is smaller than a maximum viable cell flow rate and larger than a cell settling rate.
According to an example embodiment of the second aspect, operation (a) may comprise optimizing an injection time, wherein the optimal injection time is calculated by dividing amount of the culture medium by the injection rate.
According to a third aspect, a method for cell cultivation by using the cell culture apparatus according to the first aspect is provided. The method may start with providing the culture medium to at least one of the at least two medium reservoirs and/or to at least one outlet of the at least two culture medium reservoirs in each cell culture module of the plurality of cell culture modules. Then, the method may proceed to cause, by the flow driving unit, the culture medium to flow from said one of the at least two culture medium reservoirs to the rest of the at least two culture medium reservoirs in each cell culture module of the plurality of cell culture modules for a predefined time period. The predefined time period may be selected based on the culture medium. By so doing, it may be possible to cultivate cells of the same or different types on the porous membranes of the cell culture modules under unform and controlled in vitro conditions. Moreover, the deposition of the cells on the basal surface of the porous membranes may be provided without having to invert the cell culture apparatus or to use high concentrations of the cells in the culture medium to cause the cells to bond and cover the membrane.
According to an example embodiment of the third aspect, operation (a) may comprise controlling feeding of the culture medium from the outlet of the culture medium to the flow channel by optimizing injection rate, wherein optimal injection rate for the culture medium from the outlet of the culture medium to the flow channel is smaller than a maximum viable cell flow rate and larger than a cell settling rate. The injection rate is the speed of cell suspensions being injected into the flow channel; the maximum viable cell flow rate is the maximum speed of the cell suspension or culture medium flows at which the cells will be damaged or dead if exceeded; and cell settling rate is a speed at which the cells in the culture medium will settle to the bottom of the chamber, reservoir, flow channel, and/or culture medium. The optimized injection rate may allow to provide an optimized cell loading and flow mechanism and to guide the cells to attach to the membrane area. Too high injection rate may damage the cells, too low injection rate may make the cell settle along the flow channel and/or chamber.
According to an example embodiment of the third aspect, operation (a) may further comprise optimizing an injection time, wherein the optimal injection time is calculated by dividing amount of the culture medium by the injection rate. This may allow to calculate optimal injection time using the optimal injection rate.
According to an example embodiment of the third aspect, the method may further comprise, when causing the culture medium to flow, feeding another culture medium via the first chamber towards the membrane in at least one cell culture module of the plurality of cell culture modules. By so doing, it may be possible to cultivate a first type of cells on the basal surface of the porous membranes and a different second type of cells on the apical surface of the porous membranes, thereby generating different cell co-cultures.
According to an example embodiment of the third aspect, the culture medium may be caused to flow by applying a positive pressure to the at least two culture medium reservoirs in each cell culture module of the plurality of cell culture modules for the predefined time period. By so doing, it is possible to provide a proper culture medium flow in each cell culture module, thereby improving cell cultivation on the porous membranes in each cell culture module.
According to an example embodiment of the third aspect, the culture medium may be caused to flow by applying a positive pressure to said one of the at least two culture medium reservoirs in each cell culture module of the plurality of cell culture modules for the predefined time period, while capping the rest of the at least two culture medium reservoirs. By so doing, it may be possible to provide a proper culture medium flow in each cell culture module, thereby improving cell cultivation on the porous membranes in each cell culture module.
According to an example embodiment of the third aspect, the at least two culture medium reservoirs in each cell culture module of the plurality of cell culture modules may comprise a first culture medium reservoir and a second culture medium reservoir. In this embodiment, the culture medium may be caused to flow by:
By so doing, it may be possible to provide a proper culture medium flow in each cell culture module, thereby improving cell cultivation on the porous membranes in each cell culture module.
According to a fourth aspect, a method for cell cultivation by using the cell culture apparatus according to the first aspect is provided. The method may start with providing the culture medium to one or more of the at least two medium reservoirs and/or to at least one outlet of the at least two culture medium reservoirs in each cell culture module of the plurality of cell culture modules. Then, the method may proceed to cause, by the flow driving unit, the culture medium to flow to the second chamber from said one or more of the at least two medium reservoirs in each cell culture module of the plurality of cell culture modules. After that, the cell culture apparatus may be placed in an inverted position. Next, the method may proceed to incubate the cell culture apparatus in the inverted position for a predefined time period. The predefined time period may be selected based on the culture medium. By so doing, it may be possible to cultivate cells of the same or different types on the porous membranes of the cell culture modules under unform and controlled in vitro conditions. Although the deposition of the cells on the basal surface of the porous membranes may be provided by inverting the cell culture apparatus, the method according to the fourth aspect does not require high concentrations of the cells to be used in the culture medium to cause the cells to bond and cover the membrane.
According to an example embodiment of the fourth aspect, operation (a) may comprise controlling feeding of the culture medium from the outlet of the culture medium to the flow channel by optimizing injection rate, wherein optimal injection rate for the culture medium from the outlet of the culture medium to the flow channel is smaller than a maximum viable cell flow rate and larger than a cell settling rate. The injection rate is the speed of cell suspensions being injected into the flow channel; the maximum viable cell flow rate is the maximum speed of the cell suspension or culture medium flows at which the cells will be damaged or dead if exceeded; and cell settling rate is a speed at which the cells in the culture medium will settle to the bottom of the chamber, reservoir, flow channel, and/or culture medium. The optimized injection rate may allow to provide an optimized cell loading and flow mechanism and to guide the cells to attach to the membrane area. Too high injection rate may damage the cells, too low injection rate may make the cell settle along the flow channel and/or chamber.
According to an example embodiment of the fourth aspect, operation (a) may further comprise optimizing an injection time, wherein the optimal injection time is calculated by dividing amount of the culture medium by the injection rate. This may allow to calculate optimal injection time by using the optimal injection rate.
According to an example embodiment of the fourth aspect, the method may further comprise, when causing the culture medium to flow, another culture medium may be feed via the first chamber towards the membrane in at least one cell culture module of the plurality of cell culture modules. By so doing, it may be possible to cultivate a first type of cells on the basal surface of the porous membranes and a different second type of cells on the apical surface of the porous membranes, thereby generating different cell co-cultures.
According to an example embodiment of the fourth aspect, the culture medium may comprise human brain vascular endothelial cells and said another culture medium may comprise human astrocytes. By using these types of cells, it may be possible to create artificial blood-brain barriers (BBBs) or create human mimicking artificial BBBs.
Other features and advantages of the present disclosure will be apparent upon reading the following detailed description and reviewing the accompanying drawings.
The present disclosure is explained below with reference to the accompanying drawings in which:
Various embodiments of the present disclosure are further described in more detail with reference to the accompanying drawings. However, the present disclosure may be embodied in many other forms and should not be construed as limited to any certain structure or function discussed in the following description. In contrast, these embodiments are provided to make the description of the present disclosure detailed and complete.
According to the detailed description, it will be apparent to the ones skilled in the art that the scope of the present disclosure encompasses any embodiment thereof, which is disclosed herein, irrespective of whether this embodiment is implemented independently or in concert with any other embodiment of the present disclosure. For example, apparatuses and/or methods disclosed herein may be implemented in practice using any numbers of the embodiments provided herein. Furthermore, it should be understood that any embodiment of the present disclosure may be implemented using one or more of the elements presented in the appended claims.
The word “exemplary” is used herein in the meaning of “used as an illustration”. Unless otherwise stated, any embodiment described herein as “exemplary” should not be construed as preferable or having an advantage over other embodiments.
Any positioning terminology, such as “left”, “right”, “top”, “bottom”, “above”, “under”, “apical”, “basal”, etc., may be used herein for convenience to describe one element's or feature's relationship to one or more other elements or features in accordance with the figures. It should be apparent that the positioning terminology is intended to encompass different orientations of the structure and device disclosed herein, in addition to the orientation(s) depicted in the figures. As an example, if one imaginatively rotates the structure or device in the figures 90 degrees clockwise, elements or features described as “top” and “bottom” relative to other elements or features would then be oriented, respectively, “right” and “left” relative to the other elements or features. Therefore, the positioning terminology used herein should not be construed as any limitation of the present disclosure.
Furthermore, although the numerative terminology, such as “first”, “second”, etc., may be used herein to describe various embodiments, elements or features, it should be understood that these embodiments, elements or features should not be limited by this numerative terminology. This numerative terminology is used herein only to distinguish one embodiment, element or feature from another embodiment, element or feature. For example, a first chamber discussed below could be called a second chamber, and vice versa, without departing from the teachings of the present disclosure.
In the embodiments disclosed herein, a cell may refer to a biological cell, such as a plant cell, an animal cell (e.g., a mammalian cell), a bacterial cell, a fungal cell, or the like. A mammalian cell may be, for example, from a human, a mouse, a horse, a goat, a sheep, a cow, a primate, or the like.
As used in the embodiments disclosed herein, a culture medium, also referred to as a growth medium, may refer to a liquid, suspension, or gel designed to support cellular growth in an artificial environment, i.e., in vitro. There are different types of culture media suitable for growing different types of cells. In general, the culture media may be broken into two primary categories: natural media and synthetic media. The natural media are those that are derived from tissue extraction or animal body fluids, such as plasma, lymph, and serum. The synthetic media are those created using a variety of organic and inorganic compounds. Moreover, the culture medium itself may comprise cells, bodies of cells (e.g., organoids), lipid particles, including natural or engineered (e.g., exosomal microvesicles, vacuoles, micelles or lipid particles of various design, virus particles, nanoparticles, etc.).
In the embodiments disclosed herein, a cell culture apparatus may refer to an apparatus having various wells (e.g., reservoirs, chambers, etc.) connected by microchannels in which fluids (i.e., culture media) will exhibit microfluidic behavior in their flow through the microchannels. Such a cell culture apparatus is also referred to as a microfluidic chip in this technical field. The microfluidic cell culture performed by the cell culture apparatus is generally related to cell culture, maintenance and perturbation in micro-scale fluid volumes. The reasons behind the popularity of the microfluidic cell culture are both economic and scientific. The microfluidic chips have the advantages of in vitro cell culture (high-throughput, parallel experiments, experiments may be done at the discretion of an experimenter, no need for specialized infrastructure and personnel, etc.) with in vivo like performance. For example, in mouse models, drugs are really selected for mice, not humans. By using human cells, drugs are screened for humans. Thus, using humanized microfluidic cell and tissue cultures to screen drug candidates reduces pre-clinical trial time and those drugs entering clinical testing are better suited for humans. This may reduce the probability of adverse effects and increase the chance of showing efficacy resulting in less failures in clinical trials.
In the embodiments disclosed herein, each microchannel of the cell culture apparatus is also referred to as a flow channel and may relate to a sub-millimeter-scale channel that has a hydraulic diameter below 1 mm and is used for fluidically connecting the wells of the cell culture apparatus. In other words, the microchannel or flow channel generally denotes a channel configured to pass different fluids, such, for example, as culture media (e.g., cell suspensions), reagents, or gels, in micro-scale volumes. The microchannel may be shaped such that it has appropriate flow characteristics (e.g., flow rates) depending on particular applications. For example, the microchannel may have a rectangular, e.g., square, or rounded cross-section, as well as be straight, bended, or tilted towards a required direction.
The microfluidic cell culture may involve using a porous membrane sandwiched between two flow layers within a microchannel or between a culture chamber and a microchannel for cell deposition. However, the membrane-based cell culture apparatuses known so far suffer from low throughput and incompatibility with available liquid handling systems (e.g., microtiter plate formats) and imaging systems. Furthermore, the flow control in such apparatuses is often limited to one method and not flexible enough to adapt to different resource settings. On top of that, the cell deposition on the basal (i.e., bottom) surface of the porous membrane(s) is possible in the current cell culture apparatuses only with very high cell concentrations, liquid flow control, and by inverting the cell culture apparatus.
The exemplary embodiments disclosed herein provide a technical solution that allows mitigating or even eliminating the drawbacks of the prior art. In particular, the technical solution disclosed herein provides a cell culture apparatus comprising a plurality of cell culture modules arranged adjacent to each other. Each cell culture module may comprise two or more culture medium reservoirs connected by two or more flow channels. The bottom part of the at least two culture medium reservoirs may comprise a holding member configured to be compatible with a liquid handling system. The flow channels go through a basal chamber arranged under an apical chamber. The apical and basal chambers are separated by a porous membrane. The basal chamber has a bottom part arranged higher than a bottom part of each of the culture medium reservoirs. Each cell culture module may further comprise a cavity under at least the bottom part of the second chamber. In this apparatus configuration, flows of culture media may be perfused and regulated between the culture medium reservoirs in each cell culture module by either placing the apparatus on a rocking platform or connecting the apparatus to a pneumatic pump. Moreover, the apparatus thus configured may cultivate cells of the same or different types on the basal surface of the porous membranes in the cell culture modules under uniform and controlled in vitro conditions. The deposition of the cells on the basal surface of the porous membranes may be provided without having to invert the apparatus and to use high concentrations of the cells in the culture medium.
The first culture medium reservoir 202 may have a top part with an inlet 216 for the culture medium and a bottom part with an outlet 218 for the culture medium. Similarly, the second culture medium reservoir 204 may have a top part with an inlet 220 for the culture medium and a bottom part with an outlet 222 for the culture medium. The first and second culture medium reservoirs 202 and 204 may be implemented as identical hollow tubes. Although
The bottom part of the at least two culture medium reservoirs 202, 204 of each cell culture module 106 of the plurality of cell culture modules may comprise a holding member 240 configured to be compatible with a liquid handling system 602. The holding member 240 may have a truncated cone shape. Although
According to an example embodiment, the bottom of the culture medium reservoir 202, 204 continues as the holding member 240. A top edge of the holding member 240 may comprise the outlet 218, 222 for the culture medium. The outlet 218, 222 for the culture medium may be configured to receive at least part of the liquid handling system 602. According to an example embodiment, the outlet 218, 222 for the culture medium is configured to receive at least part of the liquid handling system 602. The culture medium may be configured to be directed through the outlet 218, 222 to the flow channel 210, 212.
According to an example embodiment, the holding member 240 has a bottom edge 242 at the bottom of the culture medium reservoir 202, 204, wherein the bottom edge 242 of the holding member 240 has a larger diameter, and the top edge of the holding member 240 or the outlet 218, 222 for the culture medium has a smaller diameter. The holding member 240 may be located inside the culture medium reservoir 202, 204. Height of the holding member may increase from the bottom part of the culture medium reservoir 202, 204 towards the top part of the culture medium reservoir 202, 204 and at the same time the holding member may taper towards the outlet 218, 222 for the culture medium. The height of the holding member may fall within a range from 0.5 mm to 6 mm, for example. The bottom edge 242 of the holding member 240 may be located at the center of the bottom part of the culture medium reservoir 202, 204.
According to an example embodiment, a side 246 of the holding member 240 extends at a second tilting angle β to the first direction A starting at the bottom of the corresponding culture medium reservoir 202, 204. The tilting angle β may fall within a range of 5 degrees to 85 degrees.
According to an example embodiment, the at least one culture medium reservoir 202, 204 comprises an overflow cavity 244 between the holding member 240 and the bottom of the culture medium reservoir 202, 204. The overflow cavity 244 may be located between an outer side 246 of the holding member 240 and an inner surface of the bottom of the culture medium reservoir 202, 204. The overflow cavity 244 may store excess liquid from the liquid handling system 602, thus preventing the culture medium reservoir 202, 204 to dry out.
The first chamber 206 may be arranged between the first and second medium culture reservoirs 202 and 204 such that the first chamber 206 and the first and second culture medium reservoirs 202 and 204 are aligned with each other in a first (horizontal) direction A. The first chamber 206 may be implemented as a bottomless hollow tube, for example, with a positively tapered profile (as shown in
The second chamber 208 may be arranged under the first chamber 206 and aligned with the first chamber 206 in a second (vertical) direction B. The first direction A may be approximately perpendicular to the second direction. An angle between the first and the second direction A, B is about 90 degrees, for example. The second chamber 208 may have a cross-section corresponding to the cross-section of the first chamber 206. The second chamber 208 may have a bottom part having two or more lateral holes (not shown in
The membrane 214 may have through pores (see
The first and second flow channels 210 and 212 may be microchannels providing the passage of the culture medium between the first and second culture medium reservoirs 202 and 204 through the second chamber 208. In particular, the first flow channel 210 may connect the bottom edge 242 of the bottom part of the first culture medium reservoir 202 to one or more of the lateral holes arranged on the left side of the bottom part of the second chamber 208. The second flow channel 212 may connect the bottom edge 242 of the bottom part of the second culture medium reservoir 204 to one or more of the lateral holes arranged on the right side of the bottom part of the second chamber 208. Each of the first and second flow channels 210 and 212 may have a longitudinal section and a cross-section which allow one to achieve required flow characteristics (e.g., an appropriate flow rate). For example, each of the first and second flow channels 210 and 212 may have a variable channel height and a variable channel width which increase (e.g., gradually) towards the second chamber 208. In an example of
According to another example embodiment, the culture medium is configured to be injected through the outlet 218, 222 to the flow channel 210, 212, wherein an injection rate for the culture medium from the outlet 218, 222 of the culture medium to the flow channel 210, 212 is smaller than a maximum viable cell flow rate and larger than a cell settling rate. The injection rate for the culture medium is the speed of cell suspensions being injected into the flow channel 210, 212. The maximum viable cell flow rate is the maximum speed of the cell suspension or culture medium flows at which the cells will be damaged or dead if exceeded. The cell settling rate is a speed at which the cells in the culture medium will settle to the bottom of the chambers 206, 208, reservoirs 202, 204, flow channels 210, 212, and/or culture medium. The optimized injection rate may allow to provide an optimized cell loading and flow mechanism and to guide the cells to attach to the membrane area. Too high injection rate may damage the cells, too low injection rate may make the cell settle along the flow channel and/or the channel.
According to another example embodiment, an optimal injection time is configured to be calculated by dividing amount of the culture medium by the injection rate. The liquid handling system may be used to optimize the injection rate and/or the injection time.
In an example of
According to another example embodiment, each of the first and second flow channels 210 and 212 may be fully tilted up at the tilting angle α, starting from the bottom of the corresponding culture medium reservoir 202, 204 (i.e., there may be no first channel portion parallel to the first (horizontal) direction). According to an example embodiment, each of the at least two flow channels 210, 212 in at least one cell culture module 106 extends at a tilting angle α to the first direction A starting from the bottom or bottom edge 242 of the corresponding culture medium reservoir 202, 204. The bottom part of the second chamber 208 and at least part of the each of the at least two flow channels 210, 212 may form a cavity.
According to an example embodiment, each of the at least two flow channels 210, 212 in at least one cell culture module 106 of the plurality of cell culture modules comprising a first channel portion 300 and a second channel portion 302. The first channel portion 300 may extend from the bottom of one of the corresponding culture medium reservoirs 202, 204 and being parallel to the first direction A. The second channel portion 302 may connect the first channel portion 300 to the one of the at least two lateral holes of the second chamber 208. The second channel portion may extend at least partly at the tilting angle α to the first direction A. The bottom of the second chamber 208 and each of the second channel portions 302 of the at least two flow channels 210, 212 may form the cavity 224 under the lifted bottom part of the second chamber 208. The cavity 224 may be inverted.
According to an example embodiment, each of the at least two flow channels 210, 212 in at least one cell culture module 106 extends at a tilting angle α to the first direction A starting from the bottom of the corresponding culture medium reservoir 202, 204. The bottom part of the second chamber 208 and at least part of the each of the at least two flow channels 210, 212 may form the cavity 224.
In one embodiment, each of the second chamber 208, the first flow channel 210, and the second flow channel 212 may be coated, from inside, with a cell adhesion enhancing layer. The cell adhesion enhancing layer may be made of a hydrophilic material. Some non-restrictive examples of the hydrophilic material may include Matrigel, fibronectin, hyaluronic acid, different types of collagen (e.g., a type I collagen which is suitable for creating a blood-brain barrier cell culture model based on the apparatus 100), laminins, tenascin, elastane, nanocellulose with a host of different molecules. Such cell adhesion enhancing layers allow for less cells to be used in an experiment and more precise deposition of the cells on the basal surface of the membrane 214.
According to an example embodiment, at least part of at least one of the following is coated, from inside, with a cell repellent layer: at least one flow channel 210, 212, at least one culture medium reservoir 202, 204, first and/or second chamber 206, 208 in at least one cell culture module 106 of the plurality of cell culture modules. According to an example embodiment, the cell repellent layer being made of at least one of the following material: Teflon, Pluronic, PEG, or similar chained polymers. The cell repellent coating may be used for forming organoid on top of the membrane 214 and preventing the cells to adhere to some specific parts of the flow channels 210, 212. In some example embodiments, only the membrane areas may be used for cell adherence, which may reduce the number of cells needed and avoid non-specific binding. The cell repellent layer may be used to prevent the cells to adhere to some specific parts of the apparatus.
According to an example embodiment, a layered structure represents one possible implementation example of the cell culture module 106. The layered structure may comprise a first layer and a second layer. The first layer may comprise the first and second culture medium reservoirs 202 and 204 with holding members 240, as well as the first chamber 206. The second layer may comprise the second chamber 208 arranged exactly under the membrane 214, as well as the flow channels 210 and 212. The membrane 214 may be arranged between the first chamber 206 and the second chamber 208 to provide the fluid communication therebetween via the through pores. Moreover, the inlets of the flow channels 210 and 212 may be arranged seamlessly exactly under the outlets 218, 222 and the bottom edges 242 of the holding members 240 of the culture medium reservoirs 202 and 204, respectively, to provide the closed fluid communication between the reservoirs 202 and 204 and the flow channels 210 and 212, respectively. It should be noted that each of the first layer and the second layer may be made of room-temperature-vulcanizing (RTV) silicone (e.g., RTV615) or polydimethylsiloxane (PDMS). Moreover, the layers may be attached to each other by using adhesive or plasma bonding. The cell culture modules 106 thus configured may be attached to each other by the using the same adhesive or plasma bonding to implement the cell culture plate 102 of the apparatus 100.
According to a second embodiment, the cell culture module 106 may comprises a first culture medium reservoir 202, a second culture medium reservoir 204, a first (apical or top) chamber 206, a second (basal or bottom) chamber 208, a first flow channel 210, a second flow channel 212, a membrane 214, and a cavity 224. The first culture medium reservoir 202 may have a top part with an inlet 216 for the culture medium and a bottom part with an outlet 218 for the culture medium. Similarly, the second culture medium reservoir 204 may have a top part with an inlet 220 for the culture medium and a bottom part with an outlet 222 for the culture medium. In general, the first culture medium reservoir 202, the second culture medium reservoir 204, the second chamber 208, the first flow channel 210, the second flow channel 12, the membrane 214, the cavity 224, and the holding member 240 may be implemented in the same or similar manner as shown in
Referring back to an example of
In one embodiment, the apparatus 100 may further comprise a variety of electrodes. These electrodes may serve different purposes, and their arrangement inside the apparatus 100 depends on which purpose they are used for. In one embodiment, one or more cell culture modules of the cell culture plate 102 may comprise a first electrode arranged in the first chamber 206 and a second electrode arranged in the second chamber 208. In another embodiment, the first electrode may be arranged in the first culture medium reservoir 202 and/or the second culture medium reservoir 204 in one or more culture modules 106, while the second electrode may be arranged in the first chamber 206 of the cell culture module(s) 106. Both these embodiments with the first and second electrodes may be, for example, used to perform real-time Transepithelial/Transendothelial Electrical Resistance (TEER) measurements. In this case, the first and second electrodes may be connected to an external control unit.
Additionally or alternatively, the apparatus 100 may further comprise two or more third electrodes arranged in the first chamber 206 of one or more cell culture modules 106. These third electrodes may be arranged on the chamber walls for measuring a fluid level inside the first chamber 206. In this case, the third electrodes may either be in direct contact with the fluid/culture medium to determine the fluid level by performing conductivity measurements, or be embedded into the chamber walls (e.g., at a distance of 0.5 mm-2 mm from each other) to determine the fluid level by measuring inductive or capacitive changes in the third electrodes. At the same time, the two third electrodes may be arranged opposite to each other such that one of the two third electrodes is used to issue an ultrasound wave and another of the two third electrodes is used to receive the ultrasound wave passed through the interior of the first chamber 206 (these ultrasound measurements may be performed just like radar measurements).
Additionally or alternatively, the apparatus 100 may further comprise two or more fourth electrodes embedded into the membrane 214 of one or more cell culture modules 106. These fourth electrodes may be used to provide different stimulus signals to cells deposited on the apical and/or basal surface of the membrane.
In one embodiment, the first chamber 206 or the second chamber 208 of one or more cell culture modules 106 of the cell culture plate 102 may further comprise an oxygen sensor, a pH sensor, a CO2 sensor, or any combination thereof. These sensors may be used to enable real-time measurements of different parameters crucial for cell behavior.
The liquid handling system 602 may be used to feed the culture medium to each of the at least two culture medium reservoirs and/or to each outlet of the at least two culture medium reservoirs in each cell culture module of the plurality of cell culture modules. The liquid handling system 602 may also be used in flow driving unit 104 for pipetting the culture medium from one of the at least two culture medium reservoirs 202, 204 to another of the at least two culture medium reservoirs 202, 204 at regular time intervals or based on a level of the culture medium in each of the at least two culture medium reservoirs 202, 204.
According to an example embodiment types of liquid handling systems 602 comprise pipetting devices, pipets and micropipets, both digital and electronic, with fixed or disposable tips; microplate or microtiter plate dispensers, stackers, handlers, and washers; and a wide variety of automated robotic systems. The liquid handling systems 602 are well-known in this technical field, for which reason its description is omitted herein.
In one embodiment, the method 700 may comprise, during the operation S704, an additional operation, in which a different culture medium may be fed, e.g., by the liquid handling system 602, via the first chamber 206 towards the membrane 214 in one or more cell culture modules 106 of the cell culture plate 102. If the first chamber 206 is used, a cell monolayer may be formed on the apical surface of the membrane 214, and this cell monolayer may interact with a cell layer forming on the basal surface of the membrane 214 via the through pores of the membrane 214. If the first chamber 206 is used, multiple microcavities may be bonded to the membrane 214, for which reason cells from the different culture medium may be trapped to form a single organoid in each cavity. In this case, the flow channels 210 and 212 may perfuse the culture medium through the membrane 214 to keep the organoids alive.
In one embodiment, the operation S704 of the method 700 may be performed by applying a positive pressure to the first and second culture medium reservoirs 202 and 204 in each cell culture module 106 of the cell culture plate 102 for the predefined time period (e.g., 60 min). In another embodiment, the operation S704 of the method 700 may be performed by applying a positive pressure to the first two culture medium reservoir 202 in each cell culture module 106 of the cell culture plate 102 for the predefined time period (e.g., 60 min), while capping the second culture medium reservoir 204, or vice versa. In yet another embodiment, the operation S704 of the method 700 may be performed by: (i) applying a first positive pressure to the first culture medium reservoir 202 in each cell culture module 106 of the cell culture plate 102 for the predefined time interval, while capping the second culture medium reservoir 204; and (ii) applying a second positive pressure to the second culture medium reservoir 204 in each cell culture module 106 of the cell culture plate 102 for the predefined time interval, while capping the first culture medium reservoir 202. The selection of each of the above-indicated embodiments of the operations S704 depends on particular applications.
According to an example embodiment, the operation (a) comprises controlling feeding of the culture medium from the outlet 218, 222 of the culture medium to the flow channel 210, 212 by optimizing an injection rate, wherein the optimal injection rate for the culture medium from the outlet of the culture medium to the flow channel 210, 212 is smaller than a maximum viable cell flow rate and larger than a cell settling rate. This means that the maximum viable cell flow rate>the optimal injection rate>the cell settling rate. The injection rate is the speed of cell suspensions being injected into the flow channel 210, 212. The maximum viable cell flow rate is the maximum speed of the cell suspension or culture medium flows at which the cells will be damaged or dead if exceeded. The cell settling rate is a speed at which the cells in the culture medium will settle to the bottom of the chambers 206, 208, reservoirs 202, 204, flow channels 210, 212, and/or culture medium. The liquid handling system may be used to optimize the injection rate and/or the injection time. The optimized injection rate may allow to provide an optimized cell loading and flow mechanism and to guide the cells to attach to the membrane area. Too high injection rate may damage the cells, too low injection rate may make the cell settle along the flow channel and/or the channel.
According to another example embodiment, the operation (a) comprises optimizing an injection time, wherein the optimal injection time is calculated by dividing amount of the culture medium by the injection rate.
According to an example embodiment, similar to the method 700, in the method 800 the operation (a) comprises controlling feeding of the culture medium from the outlet 218, 222 of the culture medium to the flow channel 210, 212 by optimizing an injection rate, wherein the optimal injection rate for the culture medium from the outlet 218, 222 of the culture medium to the flow channel 210, 212 is smaller than a maximum viable cell flow rate and larger than a cell settling rate. This means that the maximum viable cell flow rate>the optimal injection rate>the cell settling rate. The injection rate is the speed of cell suspensions being injected into the flow channel 210, 212. The maximum viable cell flow rate is the maximum speed of the cell suspension or culture medium flows at which the cells will be damaged or dead if exceeded. The cell settling rate is a speed at which the cells in the culture medium will settle to the bottom of the chambers 206, 208, reservoirs 202, 204, flow channels 210, 212, and/or culture medium.
According to another example embodiment, similar to the method 700, in the method 800 the operation (a) comprises optimizing an injection time, wherein the optimal injection time is calculated by dividing amount of the culture medium by the injection rate. The liquid handling system may be used to optimize the injection rate and/or the injection time.
In one embodiment, similar to the method 700, the method 800 further comprises, during the operation S804, an additional operation, in which a different culture medium is fed, e.g., by the liquid handling system 602, via the first chamber 206 towards the membrane 214 in one or more cell culture modules 106 of the cell culture plate 102. If the first chamber 206 is used, a cell monolayer may be formed on the apical surface of the membrane 214. If the first chamber 206 is used, a single organoid is formed in each cavity of the first chamber. The culture medium may be perfused through the flow channels 210 and 212 may comprise human brain vascular endothelial cells, while the different culture medium fed to the first chamber 206 may comprise human astrocytes. By using these types of cells, it is possible to mimic an artificial blood-brain barrier (BBB).
Further features of the method directly result for example from the functionalities and parameters of the cell culture apparatus 100 and the cell culture incubator 600 as described in the appended claims and throughout the specification and are therefore not repeated here. Different variations of the methods may also be applied, as described in connection with the various example embodiments.
A cell culture apparatus may be configured to perform or cause performance of any aspect of the methods described herein.
The apparatus 100 comprising the cell culture modules like the one shown in
I. Stage of preparing the apparatus 100:
The stage of preparing was performed as follows:
The dry apparatus 100 was treated with plasma for 60 s.
The apparatus 100 was washed with 96% ethanol. 50 μL of 96% ethanol was added to each open-top (first) chamber 206.
The ethanol inside the flow channels 210, 212 and the first chamber 206 was replaced/washed twice with 50 μL of PBS.
50 μL of Col-I coating solution was injected into the flow channels 210, 212.
50 μL of Col-I coating solution was added into each first chamber 206 of the apparatus 100.
Each culture medium reservoir was filled with 50 μL PBS, closed, and incubated at 37° C., 5% CO2, for 1 hour on the rocking platform (1 cycle per 15 min).
After incubation, the coating solution in the flow channels 210, 212 and each first chamber 206 of the apparatus 100 was replaced with PBS.
The BBB model based on the mouse cells (i.e., MA-cells and MPBMEC) was obtained as follows:
4800 μL MA-cells at 2×106 cells/mL were prepared according to the conventional cell culture protocols.
The MA-cells were placed on ice.
The MA-cell loading was performed by:
4800 μL MPBMEC at 2×106 cells/mL were prepared according to the conventional cell culture protocols.
The MPBMEC were again placed on ice.
The cell culture medium (added in the apparatus in step 3e) was replaced by injecting 50 μL MPBMEC suspension at 2×106 cells/mL into the flow channels 210, 212 of the plate 102.
The plate 102 was manually rocked a few times to make sure the cell confluency is consistent.
The plate 102 was inverted and incubated at 37° C., 5% CO2, for 1 hour (static, not on the rocking platform).
100 μL MPBMEC were added to the culture medium reservoir at one side of each flow channel in the plate 102.
15 μL MPBMEC were added to the cell culture reservoir at one side of each flow channel in the plate 102.
The plate 102 was placed on the rocking platform at 37° C., 5% CO2.
The BBB model based on the human cells (i.e., HA-cells and HPBMEC) may be obtained in the same manner (one just needs to replace “MA” and “MPBMEC” with “HA” and “HPBMEC”, respectively, in operations 1-11 above).
Thus, the MAs were introduced in the first chamber 206 and grown a monolayer on the apical surface of the membrane 214, while the MPBMEC were perfused through the second chamber 208 and deposited on the basal side of the membrane 214.
Subsequently, the cells were treated immunohistochemically with antibodies against CD31, glial fibrillary acidic protein (GFAP), Actin and DAPI (which is a small molecule that binds to DNA showing the cell nuclei).
Although the exemplary embodiments of the present disclosure are described herein, it should be noted that any various changes and modifications could be made in the embodiments of the present disclosure, without departing from the scope of legal protection which is defined by the appended claims. In the appended claims, the word “comprising” does not exclude other elements, steps or operations, and the indefinite article “a” or “an” does not exclude a plurality. The mere fact that certain measures are recited in mutually different dependent claims does not indicate that a combination of these measures cannot be used to advantage.
| Number | Date | Country | Kind |
|---|---|---|---|
| 21195867.3 | Sep 2021 | EP | regional |
| 22175853.5 | May 2022 | EP | regional |
