Patent Grant
12162212
This application is the United States national phase of International Application No. PCT/EP2019/062204 filed May 13, 2019, and claims priority to German Patent Application No. 10 2018 111 751.5 filed May 16, 2018, the disclosures of which are hereby incorporated by reference in their entirety.
The disclosure relates to a method for the production of a cell culture insert with at least one membrane, in particular a biological membrane, and a cell culture insert produced according to this method.
Investigations and tests of cell cultures on a large scale are performed in multiwell plates as standard. For the cultivation of single-layer cell grasses (so-called monolayers) in such multiwell plates, suitable inserts have been developed, which are generally referred to as cell culture inserts.
Cell culture inserts are practical, permeable or semi-permeable support devices with easy applicability for the investigation of both anchorage-dependent (adherent) and anchorage-independent (non-adherent) cell lines. They are designed to create a cell culture environment that is more physiological than alternative two-dimensional culture systems.
According to the standardized sizes for multiwell plates, the diameters of the cell culture inserts are also adjusted accordingly, so that they are positioned hanging in the multiwell.
The decisive part of the cell culture insert is a membrane at the bottom/base of the cell culture insert. This membrane can have different porosities and consists of an inert plastic. Cells are seeded on this membrane in everyday laboratory work. The seeded cells normally grow into a confluent monolayer. Subsequently, barrier or penetration assays can be performed.
If the plastic membrane is removed and a biopolymer is introduced in a conventional cell culture insert, a meniscus forms due to the interfacial tension. When the polymer is cured, a cell culture insert with a concave membrane is formed. This membrane cannot or only poorly be colonized with cells, since these are pulled into the center of the cell culture insert by the combination of gravity/meniscus. This way, a cell agglomeration in the middle of the cell culture insert and no confluent monolayer is created.
The proposed solution was thus based on the object of providing a cell culture insert that has a largely flat and even biological membrane without a cone.
This object is solved with a method with features as described herein and a cell culture insert produced with this method with features as described herein.
Accordingly, a method for the preparation of a cell culture insert having at least one membrane, in particular at least one biological membrane, is provided, comprising the following steps:
According to an inventive variant, the method comprises the following steps:
The introduction of the starting materials for membrane production into the insert blank can be done in different ways. For example, the insert blank can be placed in a container containing the starting materials for membrane production. In this case, the feedstock blank is immersed in the liquid containing the starting materials.
However, it is also possible to introduce (e.g. drip in) the liquid containing the starting materials into the insert blank. In this case, it is necessary to prevent the liquid from flowing out of the interior of the insert blank by suitable covering or sealing of the openings of the insert blank.
Accordingly, the method comprises the following steps in accordance with a further variant in accordance with the solution:
In accordance with another variant in accordance with the solution, the present procedure comprises the following steps:
The insert blank used in this method is available in this variant as a separate, already prefabricated blank. The insert blank is preferably circular with a lower and an upper opening.
In a preferred embodiment, the method includes the following steps:
Thus, a method is provided with which a cone-free, flat biological membrane can be produced in a culture insert using a printer technology. This membrane is printed into an “empty” cell culture insert. For this purpose, cell culture insert blanks are provided, which can then be assembled into a biological membrane carrier by imprinting the membrane. After completion the culture insert is finished with a biopolymer membrane instead of a plastic membrane.
The advantage of a biopolymer is a better growth and an individual adaptation of the membrane to the cells to be seeded, since not every cell type can be cultivated on a plastic membrane and requires a very precise adjustment of its extracellular environment. The polymers used include all biopolymers of the so-called extracellular matrix, including collagen, hyaluronic acid, gelatine, etc.
The culture inserts that can be produced with the present method show a number of improvements over conventional cell culture inserts:
A biological membrane consisting of one or more biopolymers is provided. This provides the cells with a more physiological culture environment. The results obtained from biological experiments are much more meaningful than those that can be generated with conventional Petri dishes or cell culture inserts.
The membrane can be modified, since the physicochemical properties can be influenced by the composition of the matrix.
For example, the membrane can be generated optically transparent, which allows a non-invasive control of the cell population in real time.
Detection substances can be coupled to the matrix to detect different phenomena during the experiment.
Furthermore, different architectures can be created on the matrix.
Besides a completely flat surface, different compartments, channels etc. can be created. Furthermore, e.g. conductive elements can be pressed into the membrane to give electrical stimuli or record electrical signals from cells.
Cells, bacteria, viruses and plant germs can already be introduced into the biomembrane.
It is possible to work with more than one material type in a layer, e.g. to create areas with a modified matrix composition.
The membrane can consist of several printing layers, so that a different membrane composition can be generated not only in the X-Y plane but also in the Z plane.
The height of the membrane can be determined by the method.
In one embodiment of the present method, the insert blank used is hollow cylindrical or truncated cone shaped.
In the case of a hollow, truncated cone insert, the truncated cone has a decreasing diameter towards the lower opening (conical taper), a base surface G (upper opening) with radius R, a top surface D (lower opening) with radius r and a height hk.
The material of the insert blank is a cell- and biocompatible polymer, but especially PP, PE, PLA, PS, PC, PTFE, PVC, PMMA, PAA, PAN, PEG, PET, PU, silicones, etc.
The typical dimensions of the insert blank are based on the height and width of normal multiwell sheets. Table 1 shows the typical dimensions for conventionally used multiwall sheets.
The dimensions of the present cell culture insert are accordingly as follows (see Table 2):
The dimensions of the present culture inserts are not subject to any exact classification, as the dimensions of individual multiwell plates vary from manufacturer to manufacturer. Therefore, an average value for the culture inserts is given here.
Standard blanks or individually manufactured insert blanks can be used. The individual production enables the insert to be adapted to its function. Its size and shape can be varied. This can include, for example, the hanging on the cell culture insert or the shape of the foot. For example, the cell culture insert can be provided with an outward projection on its upper side or at its upper end so that the cell culture insert can be cultivated while hanging. In addition, the bottom side or bottom end of the cell culture insert (i.e. the part of the cell culture insert that touches the bottom of the multiwell plate) may have outwardly directed and angled projections (feet). This allows the cell culture insert to stand upright in the multiwell plate automatically.
In addition, recesses or grooves can be created in the plane of the biomatrix to achieve better adhesion to the cell culture insert. Furthermore, conductive elements can also be introduced into the cell culture insert in order to obtain signal derivation or sensory characteristics.
Furthermore, the rim of the insert blank can be continuous, so that media exchange is only possible via the membrane itself.
It is also possible to cut the rim. The cutout formed in this way can have a height that can be adjusted as desired, e.g. the cutout can be below the fill level of the cell medium present in the multiwell plate. Accordingly, the cutout can be used to supply the interior of the culture insert and to allow flow through the membrane support. In the latter case, there is no barrier function between the outer multiwell plate and the interior of the blank. Such a carrier serves the pure culture and not a barrier function.
In a further embodiment of the present method, the spacer to be placed in the insert blank is provided with at least one opening, which allows gas bubbles to be discharged from the subsequently produced membrane and thus prevents air bubbles from accumulating in the membrane. The opening should be provided at the edge of the spacer if possible.
This opening can also be described as a “bubble trap”. The Bubble Trap is a cut-out in the spacer or an empty space in the auxiliary membrane described below, which ensures that air can flow out. The air bubble created when the insert blank is inserted into the membrane polymer solution between the spacer (or auxiliary membrane) can escape in this way. If the air were to remain under the spacer or auxiliary membrane, it would be incorporated into the matrix as an air pocket, or the matrix would not have a flat surface at this point. In order to ensure a flat settlement area, an inclusion of air must be prevented. Ideally, the Bubble Trap should be slightly filled with membrane polymer solution to ensure that all air below the spacer or auxiliary membrane is displaced.
In a further embodiment of the present method, at least one spacer is designed in the form of a stamp. Such a stamp is suitable for truncated cone or hollow cylindrical insert blanks. The height or length of the stamp determines the desired distance hm to the lower opening of the insert blank and thus the thickness of the later membrane. It is advantageous if the stamp is coated on the outer surface to prevent the membrane, especially the biomembrane, from sticking when the stamp is removed.
The material of the stamp consists of a non-adhesive polymer. Non-adhesion in this case means adhesion between the placeholder/stamp and the biomembrane during and after the printing method. The material of the stamp can be PTFE, PEG or silicone.
The use of stamps enables the batch production of cell culture inserts with membranes.
In an embodiment variant, the method comprises the following steps:
When assigning insert blank and stamp, the insert blank can be put over the stamp or the stamp is inserted into the insert blank. The fastening mechanism for connecting the insert blank to the respective stamp can be a clamping mechanism (e.g. made of springs), which causes a leak-proof seal from one of the openings of the insert blank, so that the (liquid) starting materials to be subsequently introduced for membrane production remain in the insert blank and do not leak.
It is also possible to change the sequence of the method steps in the batch procedure. Thus the procedure can be carried out in the following order:
In another embodiment, at least one spacer is designed as a disc.
The material of the disc is according to the material of the stamp. The disc is made of PTFE, PEG or silicone. The diameter of the disc corresponds to the usual cell culture insert dimensions. The thickness of the disc corresponds to the desired membrane thickness between 10 μm and 1000 μm, preferably between 50 μm and 1000 μm, especially preferably between 200 and 800 μm, even more preferably between 300 and 500 μm.
Such a disc is particularly suitable for truncated cone insert blanks with diameters decreasing towards the lower opening. Preferably, the disc lies against the inner wall of the insert blank. The diameter of the disc is individually adjustable, so that the distance of the disc from the lower opening of the insert blank is determined by the diameter of the disc; i.e. the closer the disc diameter is to the radius r of the lower opening, the smaller the distance hm between the disc and the open cover surface, whereby the distance hm defines the thickness (or height) of the membrane to be produced.
In another variant of the present method, the spacer, in particular a disc-shaped spacer, is used in combination with an auxiliary membrane.
Here the auxiliary membrane is preferably formed on the upper side of the spacer (i.e. the side of the spacer facing the upper opening), in particular the disc-shaped spacer, by introducing a liquid composition containing starting materials suitable for forming the auxiliary membrane and subsequent curing (e.g. by irradiation with light or a similar physicochemical method).
The auxiliary membrane consists of a material that can be dissolved by a physico-chemical or enzymatic method, in particular PEG, poloxamer, hyaluronic acid, chitosan, chitin, collagen, etc.
The auxiliary membrane is produced in the insert blank with the help of a printer. The insert blank is inserted into a printer, e.g. the bioprinter of the company Cellbricks, and the auxiliary membrane is produced by stereolithography. This means that the blank is placed in a liquid polymer and cured by irradiation from above and below the bed.
In addition, the auxiliary membrane can be produced by using a disc as a spacer. The insert blank is dipped into a carrier with liquid auxiliary matrix, in the bottom of which the spacer, e.g. disc, is located. The diameter of the disc fills the interior of the blank flush. When in this state the liquid matrix within the insert blank is cured by irradiation from above or below the bed, a solid auxiliary membrane is created in the insert blank. If the insert blank with auxiliary membrane is pulled out of the carrier with the liquid, uncured auxiliary matrix, the spacer remains in the vessel with the liquid auxiliary matrix. In the insert blank with the auxiliary membrane, this creates a free space between the auxiliary matrix and the end of the insert blank, which can be lined with another membrane in the next step. The auxiliary membrane can be cured in such a way that a structure is created on the underside of the auxiliary membrane, which acts as a negative for shaping the membrane to be produced subsequently.
After the auxiliary membrane has cured, the spacer, especially the disc-shaped spacer, is removed so that a stable auxiliary membrane/auxiliary layer remains in the insert blank. This auxiliary membrane contains an opening for the discharge of gas bubbles (see also “Bubble Trap” as described above).
The insert blank, which is provided with at least one auxiliary membrane, can then be placed in a container containing the starting materials for producing the membrane. The membrane is formed e.g. by irradiation (see also below), and after formation of the membrane the auxiliary membrane is removed from the insert blank by suitable physicochemical methods (e.g. dissolution), leaving the formed (flat) membrane in the insert blank.
The auxiliary membrane is completely flat, since this layer was previously produced using the spacer. In addition, the auxiliary membrane contains an incision that acts as a bubble trap. Potential air bubbles that form when the biopolymer is introduced can escape through this drain and are not retained and incorporated into the biopolymer as it cures. After the biopolymer is filled in, it is cured. Subsequently, the auxiliary membrane can be dissolved by means of a physicochemical reaction, e.g. temperature increase/decrease, pH change, dissolution, etc., so that all that remains after dissolution is a flat biopolymer membrane (apart from a small ridge caused by the bubble trap).
As already mentioned several times, the membrane, and here preferably the biological membrane, is formed after immersing the culture insert with spacer in a container containing the starting materials to produce the membrane. The starting materials are especially photopolymerizable substances.
The formation of the membrane is carried out using a bio-printing method, as described in WO 2016/075103 A1.
After placing the culture insert with spacer in the container or reaction vessel containing the photopolymerizable liquid, light radiation is focused on a first focal plane which lies within a region of the reaction vessel filled with the liquid. This light radiation is then used to create a polymerized structure in the reaction vessel. The polymerized structure is located in a first layer.
Any number of additional layers can be applied to this first layer. For this purpose, a further photopolymerizable liquid is introduced into the reaction vessel, whereby the previously produced polymerized structure is at least partially covered with the further photopolymerizable liquid. Preferably, the previously produced polymerized structure is completely covered with the further photopolymerizable liquid. Now a further light irradiation is carried out in a further focal plane which lies within an area of the reaction vessel filled with the further liquid. This further focal plane thus differs from the first focal plane at least with respect to the already produced polymerized structure or with respect to the layer of this polymerized structure.
The aforementioned steps of introducing a further photopolymerizable liquid, focusing light on a further focal plane, and producing a further polymerized structure in a further layer can now be repeated at will with further photopolymerizable liquids until the desired membrane is produced.
The layer thickness of the membrane to be produced can be adjusted as desired and adapted to the corresponding requirements. For example, the layer thickness of the membrane can be between 10 μm and 1000 μm, preferably between 50 and 1000 μm, especially preferably between 200 and 800 μm, even more preferably between 300 and 500 μm, e.g. between 310 and 325 μm.
The photopolymerizable liquid can also contain biological cells or other substances. If polymerization occurs as a result of light irradiation, the cells contained in the liquid are embedded in a corresponding polymer.
This printing method can be used to produce membranes from any polymer, preferably biopolymers.
Accordingly, the membrane can be made of the following materials or comprise: technical biopolymers, such as gelatine; alpha- and beta-polysaccharides, such as pectins, chitin, callose and cellulose; lipids, in particular membrane-forming lipids, such as phospholipids, sphingolipids, glycolipids and ether lipids; polyhydroxyalkanoates; biobased polymers, such as polylactide, polyhydroxybutyrate petroleum-based polymers, such as polyesters, in particular polyethylene glycol, polyvinyl alcohol, polybutylene adipate terephthalate (PBAT), polybutylene succinate (PBS), polycaprolactones (PCL), polyglycolide (PGA); synthetic peptides, such as recombinantly produced amino acids, amides; components of the extracellular matrix, such as collagens, fibrillin, elastin, glycosaminoglycans, in particular hyaluronic acids, heparan sulfate, dermatan sulfate, chondroitin sulfate and keratan sulfate. Preferred membrane materials are collagens, hyaluronic acid, chitosan, gelatine, PLA, PEG and combinations thereof.
In one example, the membrane consists of gelatine and collagen as additives. A suitable photoinitiator such as lithium phenyl-2,4,6-trimethylbenzoylphosphinate (LAP) is used to produce the starting materials.
In another embodiment, a safety device is provided for holding the membrane in place during use. It is preferred if the at least one securing means is in the form of a carrier consisting of different structures adapted to the membrane material, in particular of grid-shaped or spoke-shaped structures.
In a further method variant, the cell culture insert is formed from the insert blank and membrane in one piece using the printing method described above (one-pot synthesis). In analogy to the method described in WO 2016/075103 A1, the one-pot synthesis is performed additively with photopolymerizable materials. First, the base of the scaffold is printed from a first (cell-repellent) biomaterial. Subsequently, a biocompatible layer is produced from a second biomaterial. In the last step, the scaffold is completed by the edges. Both materials are processed in a single printing method.
The insert blank formed in this method comprises a (top) opening and can include a bottom. The insert blank is preferably made of a first cell-repellent biomaterial or biopolymer, such as polyethylene glycol (PEG) or one of the other possible polymer materials mentioned above for the insert blank. On the bottom of the insert blank another biocompatible and biofunctional biopolymer is incorporated as a membrane, e.g. made of gelatine, on which cell materials can grow. The combination of the two different materials creates a scaffold that can be specifically seeded with cells on the biocompatible material.
In the course of a longer cultivation period, the biomembrane may change, e.g. shrinkage or alteration by cells. In this case, the safety device, e.g. a grid, prevents the biomembrane from slipping or falling out of the culture insert. In its simplest form, the securing agent can be placed on the underside of the cell culture insert, i.e. the side that supports the membrane. The support of the securing device, e.g. a grid, is based on a simple press fit. In order to remove the locking device (and the membrane) from the culture insert afterwards, the press fit can be removed again, e.g. with a kind of cap lifter. In this case, the press fit is simply levered off.
As already mentioned above, it is possible to produce a biological membrane in a blank from two or more polymeric materials, preferably biopolymers. The materials can be arranged in different architectures. Thus, the different polymer materials can be arranged on top of each other in layers, whereby the number of layers can be freely selected. In one variant, one layer of a first polymer and one layer of a second polymer is provided. It is also conceivable that the polymer materials are arranged next to each other in one layer. Thus, a membrane section of a first polymer material can be provided in a variant, whereby the membrane section is integrated into the second polymer material (centrally), i.e. the membrane section of the first polymer material is surrounded by the second polymer material.
In a further embodiment, a three-dimensional architecture of the membrane is planned. For this purpose the membrane can be printed using a geometric form. In this way, e.g. villi, channels, hills, valleys, etc.,—also made of different materials—can be inserted. Thus, the membrane surface to be colonized can be formed with regular or irregular structures (hills, valleys).
In one embodiment at least one channel can be inserted into the membrane. The channel can be used e.g. to supply the inner compartment of the blank. The channel acts as a medium carrier with nutrient medium, which is rinsed through the channel. Cells, which are settled on the membrane in the interior of the compartment, can be supplied from the channels through the membrane.
It is still possible to introduce functional material into the membrane. For example, an additional detector, dye, enzyme, chemokine, nanoparticles or similar can be integrated into the membrane during the printing method. Over time, this material can be used for online monitoring of the cell culture. For example, cell death can be detected by a fluorescent dye or the current oxygen saturation or pH value. The functional material may or may not have contact to the inner and outer boundary layer. The functionalization can be observed by a color change, irradiation or other detectable measurement. The functional material can be inserted pointwise into the membrane material, or it can be provided in the membrane in a flat or layered form.
It is also possible and imaginable to divide the membrane surface e.g. into segments, print cell arrays or introduce gradients. Hereby it is possible to structure the membrane exactly in its thickness and surface.
Furthermore, the optical transparency can be influenced by the formulation of the biomatrix. For example, a transparent matrix can be created that allows optical control of the cell population. Thus, the transparency allows a non-invasive control of the cell population, which is not possible with a conventional cell culture application.
In addition, a (non-polymeric) further material can be introduced into the membrane and/or the blank in a defined manner. In this way, further functions can be realized, e.g. by introducing sensors, detection, conductive materials, chemicals, nanoparticles, etc.
In one embodiment, the blank is provided with at least one probe. The at least one probe, preferably two probes, can be provided on the inside and outside of the blank. By using probes, the electrical resistance can be determined, allowing conclusions to be drawn about the density of the membrane and the cell turf.
With the present method, a cell culture insert can now be produced which consists of an insert blank with at least one membrane arranged therein, in particular at least one biomembrane, wherein the at least one membrane is flat and does not have a cone; i.e. a cell culture insert with a confluent monolayer can be provided with this method.
The present cell culture insert can be used for the cultivation of different cell lines and subsequent performance of barrier or penetration assays.
Suitable target lines are all cells and cell lines that represent a barrier function, e.g. endothelial cells, trophoblasts, astrocytes, enterocytes etc. or cells and cell lines that represent a metabolic function, e.g. hepatocytes, cardiomyocytes, myocytes etc. In general, all cell types that are adherent are suitable.
The proposed solution is explained below with reference to the FIGS. by means of several examples. It shows:
On the right side b) of
In a second subsequent step, the culture insert with the stamp inserted therein is placed in a reaction vessel containing a polymerizable liquid, the polymerizable liquid containing the starting components for the production of the desired biomembrane. The stamp should contain an opening (“bubble trap”) to prevent the accumulation of air bubbles in the biomembrane.
In the next, third step of the method, the biomembrane is formed in a printing method, whereby light is irradiated onto the polymerizable liquid in a focal plane, resulting in polymerization to the biomembrane in the focal plane.
After curing of the biomembrane, the stamp can be easily removed from the culture insert due to its material coating (step 4), leaving a flat biomembrane in the culture insert.
In the embodiment of the method shown in
In the method embodiment shown in
The fourth embodiment of the method shown in
After the auxiliary membrane has cured, the disc is removed again as a spacer in a third step, leaving behind a stable auxiliary membrane with an opening as a “bubble trap”.
In the next, fourth step, the culture insert with the auxiliary membrane is placed in a reaction vessel containing the liquid biopolymer and then cured by irradiation in a printing method.
After hardening of the biomembrane and removal of the culture insert from the reaction vessel, a bilayer of biomembrane and auxiliary membrane remains in the culture insert. In a final step, the auxiliary membrane is removed by a physicochemical method or simple dissolution, leaving behind a flat biomembrane.
To prevent the printed membrane layer from falling out, a plastic grid can be placed under the culture insert after the biomembrane has been manufactured (see
An embodiment of a cell culture insert manufactured according to the solution is shown in
Depending on the membrane material, different cells can colonize the biomembrane and form monolayers (see
The illustrations of
The microscopic images shown in
In the following two images, the markers ITGB1 (right) and aPKC (bottom left) were examined, which also document a polarization towards or away from the membrane.
The present cell culture insert can be designed with a continuous rim (
The cell culture insert can be provided with two or more different materials as a membrane in a blank, whereby the materials can be arranged in different architectures, e.g. side by side (
In another variant of the cell culture insert, the membrane is printed with a geometric shape. The membrane must not only be inserted straight into the blank, but can also have an architectural shape. For example, villi, channels, hills, valleys (
A channel may be introduced into the membrane of the cell culture insert, which can be flushed from outside the blank (
Functional material may also be incorporated into the membrane of the cell culture insert. For example, an additional detector, dye, enzyme, chemokine, nanoparticles or similar can be integrated into the membrane during the printing method. Over time, this material can be used for online monitoring of the cell culture. For example, cell death can be detected by a fluorescent dye or the current oxygen saturation or pH value. The functional material may or may not have contact to the inner and outer boundary layer. The functionalization can be observed by a color change, irradiation or other detectable measurement. The functional material can be introduced pointwise into the membrane (
The cell culture insert can also enable the measurement of membrane density by electrical resistance. In this case, a special blank can be used in which a probe is attached to the inside and outside of the blank in order to measure the electrical resistance and thus draw conclusions about the density of the membrane and the cell layer (
Cell culture inserts with a diameter of 12 mm were produced using the stamping method. A gelatine matrix with a concentration of 10% (W/V) was used, mixed with LAP as initiator in a concentration of 0.1% (W/V). Furthermore, collagen I was used as an additive.
The blank was filled with a silicone stamp and placed in a basin in the printer containing the liquid gelatine matrix described above, so that the blank rests on the bottom of the basin in the printer. To create a membrane of 500 μm, the distance was adjusted accordingly with the stamp before.
Subsequently, the gelatine matrix was cured by irradiation with a wavelength of 385 nm. After hardening, the carrier was removed from the basin and the printer. In addition, the stamp was removed, leaving behind a cell culture insert with the previously defined height and with a flat surface for colonization.
Two different cell culture inserts were produced. A first insert with a membrane with collagen I as an additive and a second insert with a membrane without this additive. In this case the gelatine membrane was made transparent and could be examined optically.
After production of the cell culture inserts with biological membrane, they were colonized with Vero cells. This is a kidney cell line of the green monkey. This cell line is often used for infection experiments. After colonization, the Vero cells formed a confluent monolayer over the entire surface of the cell culture insert.
After colonization, a GFP-tagged cowpox strain was used to infect the Vero cells with the strain. The spread of the infection could be studied and observed by the fluorescent viruses and the transparent cell culture insert over the course of the experiment of 28 days.
After the experiment, the membrane was stamped out and deep-frozen. In addition, the membrane could be cut and stained with the usual histological methods, so that a histological follow-up was possible.
| Number | Date | Country | Kind |
|---|---|---|---|
| 10 2018 111 751.5 | May 2018 | DE | national |
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/EP2019/062204 | 5/13/2019 | WO |
| Publishing Document | Publishing Date | Country | Kind |
|---|---|---|---|
| WO2019/219605 | 11/21/2019 | WO | A |
| Number | Name | Date | Kind |
|---|---|---|---|
| 10299940 | Kloke | May 2019 | B2 |
| 20160136895 | Beyer | May 2016 | A1 |
| 20190143002 | Denda et al. | May 2019 | A1 |
| Number | Date | Country |
|---|---|---|
| 2548943 | Jan 2013 | EP |
| 3476933 | May 2019 | EP |
| 2016057571 | Apr 2016 | WO |
| 2016075103 | May 2016 | WO |
| 2016179242 | Nov 2016 | WO |
| 2017222065 | Dec 2017 | WO |
| 2018064323 | Apr 2018 | WO |
| Entry |
|---|
| Duregger et al., “Additive-manufactured microporous polymer membranes for biomedical in vitro applications”, Journal of Biomaterials Applications, 2018, 18 pages. |
| Femmer et al., “Print your own membrane: direct rapid prototyping of polydimethylsiloxane”, Lab on a Chip, 2014, 12 pages. |
| Horvath et al., “Engineering an in vitro air-blood barrier by 3D bioprinting”, Scientific Reports, 2015, 17 pages. |
| Low et al., “Perspective on 3D printing of separation membranes and comparison to related unconventional fabrication techniques”, Journal of Membrane Science, 2017, pp. 596-613. |
| Number | Date | Country | |
|---|---|---|---|
| 20210107212 A1 | Apr 2021 | US |
