Patent Application
20240384241
The present disclosure relates generally to the field of biotechnology. 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 that enables high-throughput microfluidic cell culture.
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 comprises a plurality of cell culture modules arranged adjacent to each other. Each cell culture module of the plurality of cell culture modules comprises at least two culture medium reservoirs, a first chamber, a second chamber, a membrane, and at least two flow channels. Each of the at least two culture medium reservoirs has 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 is arranged between the at least two culture medium reservoirs such that the first chamber and the at least two culture medium reservoirs are aligned with each other in a first direction. The second chamber is arranged under the first chamber and aligned with the first chamber in a second direction. The second direction is perpendicular to the first direction. The second chamber has a bottom part having at least two lateral holes. The bottom part of the second chamber is arranged higher than the bottom part of each of the at least two culture medium reservoirs. The membrane has through pores formed therein and is 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 connects 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 further comprises 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. 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.
In one embodiment of the first aspect, the first chamber in at least one cell culture module of the plurality of cell culture modules is implemented as a bottomless hollow tube. With this first chamber, it is 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.
In one embodiment of the first aspect, the first chamber in at least one cell culture module of the plurality of cell culture modules is implemented as a hollow tube having a curved or angled bottom. In this embodiment, the curved or angled bottom has at least one cavity and at least one hole formed in each of the at least one cavity. With this first chamber, it is possible to deposit cells on separate portions of the apical surface of the porous membrane. This configuration of the first chamber is 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.
In one embodiment of the first aspect, the curved or angled bottom is coated, from outside, with a cell adhesion enhancing layer such that the at least one hole of the at least one cavity remains 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 means less cell death or, in other words, more healthy cells in the cell culture as dead cells tend to release factors promoting apoptosis.
In one embodiment of the first aspect, the second chamber has a height falling within a range from 50 micrometers (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.
In one embodiment of the first aspect, the second chamber in at least one cell culture module of the plurality of cell culture modules is 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 allows 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 means less cell death or, in other words, more healthy cells in the cell culture as dead cells tend to release factors promoting apoptosis.
In one 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 is 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) becomes stronger, cell proliferation is appropriate to a tissue being modelled, and cell viability is better. Selecting the correct adhesion enhancing layer also plays a role in the proper communication between cell types. Thus, this coating layer allows 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 means less cell death or, in other words, more healthy cells in the cell culture as dead cells tend to release factors promoting apoptosis.
In one embodiment of the first aspect, the flow driving unit is 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 is 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).
In one 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 is implemented as a hollow tube. With such configuration, the culture medium reservoirs are easier and cheaper to manufacture.
In one embodiment of the first aspect, the bottom part of each of the at least two culture medium reservoirs has a positively tapered profile. By using such a configuration of the culture medium reservoirs, it is 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 is left in the culture medium reservoirs. This also helps to reduce the number of cells that is 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.
In one embodiment of the first aspect, at least one cell culture module of the plurality of cell culture modules further comprises 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.
In another embodiment of the first aspect, at least one cell culture module of the plurality of cell culture modules further comprises 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.
In one embodiment of the first aspect, at least one cell culture module of the plurality of cell culture modules further comprises 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.
In one embodiment of the first aspect, at least one cell culture module of the plurality of cell culture modules further comprises 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.
In one embodiment of the first aspect, at least one cell culture module of the plurality of cell culture modules further comprises at least one of an oxygen sensor, a pH sensor and a CO2 sensor in the first chamber or the second chamber. These sensors enable real-time measurements of parameters crucial for cell behavior.
In one embodiment of the first aspect, each of the at least two flow channels extend at least partly at a tilting angle to the first direction. In this embodiment, the tilting angle fall within a range of 5 degrees to 45 degrees. With such titled flow channels, it is possible to achieve appropriate flow characteristics and, therefore, improve cell delivery to the second chamber.
In one embodiment of the first aspect, the through pores of the membrane has an average pore size falling within a range from 0.2 am to 10 μm. By varying the average pore size within this range, it is possible to study the behavior of cells of different sizes, which are deposited on one or each of the apical and basal surfaces of the membrane.
In one 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 has a variable channel height and a variable channel width which increase towards the second chamber. 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 and, consequently, the cell attachment to the basal surface of the porous membrane.
In one 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.
In one 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 comprises a first channel portion and a second channel portion. The first channel portion extends from the outlet of the bottom part one of the at least two culture medium reservoirs and is parallel to the first direction. The second channel portion connects the first channel portion to one of the at least two lateral holes of the second chamber. The second portion is tilted relative to the first direction. 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 a second aspect, a cell culture incubator is provided. The cell culture incubator comprises the cell culture apparatus according to the first aspect, and a pipetting station configured to feed the culture medium to each of the at least two culture medium reservoirs in each cell culture module of the plurality of cell culture modules. 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 a third aspect, a method for cell cultivation by using the cell culture apparatus according to the first aspect is provided. The method starts with the step of providing the culture medium to one of the at least two medium reservoirs in each cell culture module of the plurality of cell culture modules. Then, the method proceeds to the step of causing, 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 is selected based on the culture medium. By so doing, it is 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.
In one embodiment of the third aspect, the method further comprises, during the step of causing the culture medium to flow, the step of 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 is 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.
In one embodiment of the third aspect, the culture medium is 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.
In yet another embodiment of the third aspect, the culture medium is 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 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.
In yet another embodiment of the third aspect, the at least two culture medium reservoirs in each cell culture module of the plurality of cell culture modules comprises a first culture medium reservoir and a second culture medium reservoir. In this embodiment, the culture medium is caused to flow by:
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 a fourth aspect, a method for cell cultivation by using the cell culture apparatus according to the first aspect is provided. The method starts with the step of providing the culture medium to one or more of the at least two medium reservoirs in each cell culture module of the plurality of cell culture modules. Then, the method proceeds to the step of causing, 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 method goes on to the step of placing the cell culture apparatus in an inverted position. Next, the method proceeds to the step of incubating the cell culture apparatus in the inverted position for a predefined time period. The predefined time period is selected based on the culture medium. By so doing, it is 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 is 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.
In one embodiment of the fourth aspect, the method further comprises, during the step of causing the culture medium to flow, the step of 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 is 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.
In one embodiment of the fourth aspect, the culture medium comprises human brain vascular endothelial cells and said another culture medium comprises human astrocytes. By using these types of cells, it is 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 comprises two or more culture medium reservoirs connected by two or more flow channels. 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. 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 has 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 has 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 first chamber 206 is 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. 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 is arranged under the first chamber 206 and aligned with the first chamber 206 in a second (vertical) direction. The second chamber 208 may have a cross-section corresponding to the cross-section of the first chamber 206. The second chamber 208 has a bottom part having two or more lateral holes (not shown in
The membrane 214 has through pores (see
The first and second flow channels 210 and 212 are 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 connects the outlet 218 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 connects the outlet 222 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 a variable channel height and a variable channel width which increase (e.g., gradually) towards the second chamber 208.
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.
At the same time, unlike the first chamber 206, the first chamber 506 may be implemented as a hollow tube having a curved or angled bottom. As shown in
Referring back to
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 (506) and a second electrode arranged in the second chamber 208 (508). In another embodiment, the first electrode may be arranged in the first culture medium reservoir 202 (502) and/or the second culture medium reservoir 204 (504) in one or more culture modules 106, while the second electrode may be arranged in the first chamber 206 (506) 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 (506) 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 (506). 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 (506) (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 (514) 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 (506) or the second chamber 208 (508) 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.
In one embodiment, the method 700 may comprise, during the step $704, an additional step, in which a different culture medium is fed, e.g., by the pipetting station 602, via the first chamber 206 (506) towards the membrane 214 (514) in one or more cell culture modules 106 of the cell culture plate 102. If the first chamber 206 is used, a cell monolayer is formed on the apical surface of the membrane 214, and this cell monolayer interacts 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 506 is used, multiple microcavities 524 are bonded to the membrane 514, for which reason cells from the different culture medium are trapped to form a single organoid in each cavity. In this case, the flow channels 510 and 512 may perfuse the culture medium through the membrane 514 to keep the organoids alive.
In one embodiment, the step S704 of the method 700 may be performed by applying a positive pressure to the first and second culture medium reservoirs 210 (510) and 212 (512) 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 step S704 of the method 700 may be performed by applying a positive pressure to the first two culture medium reservoir 202 (502 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 (504), or vice versa. In yet another embodiment, the step S704 of the method 700 may be performed by: (i) applying a first positive pressure to the first culture medium reservoir 202 (502) 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 (504); and (ii) applying a second positive pressure to the second culture medium reservoir 204 (504) 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 (502). The selection of each of the above-indicated embodiments of the step S704 depends on particular applications.
In one embodiment, similar to the method 700, the method 800 further comprises, during the step S804, an additional step, in which a different culture medium is fed, e.g., by the pipetting station 602, via the first chamber 206 (506) towards the membrane 214 (514) in one or more cell culture modules 106 of the cell culture plate 102. If the first chamber 206 is used, a cell monolayer is formed on the apical surface of the membrane 214. If the first chamber 506 is used, a single organoid is formed in each cavity 524 of the first chamber 506. The culture medium perfused through the flow channels 210 (510) and 212 (512) may comprise human brain vascular endothelial cells, while the different culture medium fed to the first chamber 206 (505) may comprise human astrocytes. By using these types of cells, it is possible to mimic an artificial blood-brain barrier (BBB).
The apparatus 100 comprising the cell culture modules like the one shown in
The stage of preparing was performed as follows:
The BBB model based on the mouse cells (i.e., MA-cells and MPBMEC) was obtained as follows:
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 steps 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 |
This application is a national phase entry of, and claims priority to, International Patent Application No. PCT/EP2022/075131 (filed 9 Sep. 2022), which claims priority to European Patent Application No. 21195867.3 (filed 9 Oct. 2021), the entire disclosures of which are incorporated herein by reference.
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/EP2022/075131 | 9/9/2022 | WO |
