Patent Application
20200032183
The present invention relates to a method for manufacturing a cell structure which includes a biocompatible macromolecular block and a cell and in which the plurality of biocompatible macromolecular blocks are disposed in gaps between the plurality of cells.
Currently, regenerative medicine, which regenerates living body tissues and organs having functional disorders or dysfunction, is put into practical use. The regenerative medicine is new medical technology creating a form or a function of a living body tissue that cannot be recovered with only natural healing ability possessed by a living body, which is the same as that of an original tissue, again, using three factors including a cell, a scaffold, and a growth factor. In recent years, treatment using cells is gradually realized. Examples thereof include cultured epidermis using autologous cells, a cartilage treatment using autologous chondrocytes, a bone regeneration treatment using mesenchymal stem cells, a cardiomyocyte sheet treatment using myoblasts, a cornea regeneration treatment using a corneal epithelial sheet, and a nerve regeneration treatment. These new treatments are intended to repair and regenerate a living tissue, unlike alternative medicine by an artificial object (for example, artificial bone substitutes and hyaluronic acid injection) in the related art, and can achieve high therapeutic effects. In practice, products such as cultured epidermis and cultured cartilage using autologous cells have been commercially available.
In WO2011/108517A, a cell structure that includes a macromolecular block having biocompatibility and a cell and in which the plurality of macromolecular blocks are disposed in gaps between the plurality of cells is disclosed. In the cell structure disclosed in WO2011/108517A, nutrient from the outside to the inside of the cell structure can be delivered, the cell has a sufficient thickness, and cells are uniformly present in the structure. In the example of WO2011/108517A, high cell survival activity is demonstrated by using a macromolecular block formed of recombinant gelatin or a natural gelatin material.
In JP2014-012114A, a cell structure for cell transplantation that includes a macromolecular block having biocompatibility and at least one type of cells and in which the plurality of macromolecular blocks are disposed in gaps between the plurality of cells is disclosed.
In WO2014/133081A, a cell structure for cell transplantation which includes biocompatible macromolecular blocks not including glutaraldehyde and at least one kind of cells and in which the plurality of biocompatible macromolecular blocks are disposed in gaps between the plurality of cells, wherein a tap density of the biocompatible macromolecular blocks is 10 mg/cm3 to 500 mg/cm3, or a value obtained by dividing a square root of a cross sectional product in a two-dimensional cross sectional image of the macromolecular blocks by a perimeter is 0.01 to 0.13 is disclosed.
In WO2011/108517A, JP2014-012114A, and WO2014/133081A, manufacturing methods in a small scale of manufacturing one cell structure that includes macromolecular blocks having biocompatibility and cells and in which the plurality of macromolecular blocks are disposed in gaps between the plurality of cells per one well are disclosed.
On the other hand, WO2012/036011A discloses a culture substrate in which a plurality of recessed portions forming compartments in which an object to be cultured is cultured are formed on the surface of the culture substrate, and the surface of the culture substrate between the recessed portions adjacent to each other is a non-flat surface, and discloses that spheroid culture is carried out using this culture substrate.
JP2015-073520A discloses a cell culture container for performing spheroid culture which includes: a culture surface on which a plurality of recessed portions forming compartments in which an object to be cultured is cultured are formed; a container main body including the culture surface on a bottom surface, and a liquid-permeable lid body which is placed on the top portions of the plurality of recessed portions and closes the openings of the recessed portions, in which the top portion of the culture surface between the recessed portions adjacent to each other, the liquid-permeable lid body is disposed so that the distance from the top portion between the recessed portions in a state of being immersed in a culture liquid in the container main body is smaller than the outer diameter dimension of the object to be cultured which has been cultured in the recessed portions.
In a case of being used in repair and regeneration of a living tissue, for example, it is desirable to simultaneously manufacture cell structures in large quantities, for example, 1,000 or more cell structures in some cases. As a method of culturing a large amount of cell mass, a method of suspending and stirring the cell mass in a medium has been known. However, the inventors of the present invention have been found that, in a case where a suspending, stirring, and culturing method is used for manufacturing of a cell structure, there are problems in that, (1) the formation efficiency of the cell structure is poor (that is, a cell structure is not formed, and a ratio of the macromolecular blocks and the cells which are individually present is large), (2) a ratio of the macromolecular blocks and the cells in the obtained cell structure varies for each cell structure, and (3) sizes of the cell individual structures are different from each other. In a case where the cell structure is used for repair and regeneration of a living tissue, it is desirable that the cell structure is homogeneous (for example, a ratio, a shape, or a size of macromolecular blocks and cells is homogeneous) in order to obtain an excellent therapeutic effect.
An object of the present invention is to provide a method of manufacturing a large amount of uniform cell structures that include biocompatible macromolecular blocks and cells and in which the plurality of biocompatible macromolecular blocks are disposed in gaps of the plurality of cells for a short period of time.
The inventors of the present invention have diligently researched to achieve the above object to find that it is possible to manufacture a large amount of uniform cell structures for a short period of time by adding a mixture of biocompatible macromolecular blocks, cells, and a liquid medium to a first culture container having a culture surface on which the plurality of recessed portions are formed and a side wall part standing on an outer periphery of the culture surface and allowing the first culture container to stand, so as to form cell structures, and then stirring and culturing the cell structures in a second culture container comprising stirring means. The present invention has been completed based on the finding.
That is, according to the present invention, the following inventions are provided.
(1) A method of manufacturing a cell structure, comprising: a step (A) of adding a mixture of biocompatible macromolecular blocks, cells, and a liquid medium to a first culture container having a culture surface on which a plurality of recessed portions are formed and a side wall part standing on an outer periphery of the culture surface such that a liquid surface of the mixture is over the culture surface;
a step (B) of allowing a first culture container of the step (A) to stand and forming a cell structure which includes the biocompatible macromolecular block and the cell in the recessed portion and in which the plurality of biocompatible macromolecular blocks are disposed in gaps between the plurality of cells; and a step (C) of stirring and culturing a content of the first culture container obtained in the step (B) in a second culture container comprising stirring means.
(2) The method of manufacturing a cell structure according to (1), in which the first culture container is allowed to stand in the step (B) until free biocompatible macromolecular blocks are 30 mass % or less of the total biocompatible macromolecular blocks.
(3) The method of manufacturing a cell structure according to (1) or (2), in which the first culture container is allowed to stand in the step (B) for a period of time for which a ratio of the number of cell structures manufactured after the step (C) to the number of recessed portions is 70% or more.
(4) The method of manufacturing a cell structure according to any one of (1) to (3), in which a size of the biocompatible macromolecular block is 1 μm to 700 μm.
(5) The method of manufacturing a cell structure according to any one of (1) to (4), in which a treatment for suppressing cell adhesion is performed on the culture surface and a surface of the recessed portion.
(6) The method of manufacturing a cell structure according to any one of (1) to (5), in which a depth of the recessed portion is 2 to 100 times of a size of the biocompatible macromolecular block, and a diameter of the recessed portion is 2 to 100 times of a size of the biocompatible macromolecular block.
(7) The method of manufacturing a cell structure according to any one of (1) to (6), in which a period of time for which the first culture container is allowed to stand is 2 hours to 24 hours.
(8) The method of manufacturing a cell structure according to any one of (1) to (7), in which stirring and culturing time for which a content of the first culture container in the step (C) is 12 hours to 93 hours.
(9) The method of manufacturing a cell structure according to any one of (1) to (8), in which the biocompatible macromolecule is gelatin.
(10) The method of manufacturing a cell structure according to (9), in which the gelatin is represented by the following formula.
A-[(Gly-X-Y)n]m-B Formula:
in the formula, A represents random amino acid or an amino acid sequence, B represents any amino acid or amino acid sequence, n X's each independently represent any one of amino acid, n Y's each independently represent any one of any amino acid, n represents an integer of 3 to 100, and m represents an integer of 2 to 10, and also n Gly-X-Y's may be identical to or different from each other.
(11) The method of manufacturing a cell structure according to (9) or (10), in which the gelatin is any one of a peptide including an amino acid sequence described in SEQ ID NO: 1;
a peptide having biocompatibility and including an amino acid sequence in which one
or more amino acids are deleted, substituted, or added in an amino acid sequence described in SEQ ID NO: 1; or
a peptide which is formed of an amino acid sequence having 80% or more sequence identity to the amino acid sequence described in SEQ ID No: 1, and has biocompatibility.
According to a method of manufacturing a cell structure of the present invention, it is possible to manufacture a large amount of uniform cell structures that include biocompatible macromolecular blocks and cells and in which the plurality of biocompatible macromolecular blocks are disposed in gaps of the plurality of cells for a short period of time.
Hereinafter, an embodiment of the present invention will be described in detail.
A method of manufacturing a cell structure according to the embodiment of the present invention includes
a step (A) of adding a mixture of biocompatible macromolecular blocks, cells, and a liquid medium, to a first culture container having a culture surface, on which a plurality of recessed portions are formed, and a side wall part standing on an outer periphery of the culture surface such that a liquid surface of the mixture is over the culture surface;
a step (B) of allowing a first culture container of the step (A) to stand and forming a cell structure which includes the biocompatible macromolecular block and the cell in the recessed portion and in which the plurality of biocompatible macromolecular blocks are disposed in gaps between the plurality of cells; and
a step (C) of stirring and culturing a content of the first culture container obtained in the step (B) in a second culture container comprising stirring means.
In the manufacturing method according to the embodiment of the present invention, it is possible to add the mixture of the biocompatible macromolecular blocks, the cells, and the liquid medium, to the first culture container having the culture surface on which the plurality of recessed portions are formed and a side wall part standing on the outer periphery of the culture surface such that the liquid surface of the mixture is over the culture surface, and adding the biocompatible macromolecular block, the cell, the liquid medium to all of the recessed portions of the first culture container in one step. According to the method of the embodiment of the present invention, a cell structure can be manufactured in a short period of time.
According to the present invention, in the recessed portion of the first culture container, a cell structure which includes biocompatible macromolecular blocks and cells and in which the plurality of biocompatible macromolecular blocks are disposed in gaps between the plurality of cells, and then a content of the first culture container is stirred and cultured in the second culture container comprising the stirring means. With respect to the cell structure obtained after the stirring culture step, for example, at least one of a ratio, a shape, or a size of the macromolecular block having biocompatibility are uniform. The expression “at least one of a ratio, a shape, or a size are uniform” does not mean that at least one of the ratio, the shape, or the size are completely the same, but means that at least one of the ratio, the shape, or the size are more uniform than those in a case where a cell structure is manufactured under conditions provided in Comparative Examples 1 to 3 below.
In the present invention, in a case where the cell structure is stirred and cultured, sufficient nutrient and oxygen can be delivered to the cells in the cell structure together with preventing fusion and disintegration of the cell structures, and thus it is possible to manufacture a cell structure having excellent cell viability.
In a case where the mixture of the biocompatible macromolecular blocks, the cells, and the liquid medium is added such that the liquid surface of the mixture is over the culture surface of the first culture container, the macromolecular block and the cell in which a cell structure is not formed on the upper surface between the recessed portions of the culture surfaces are present. Even in this case, by stirring and culturing the cell structure, the macromolecular block and the cell that do not form the cell structure are introduced into the cell structure, so as to form a larger cell structure. The physical force of stirring strengthens the adhesion between the macromolecular block and the cell which are included in the cell structure.
As above, in the method according to the embodiment of the present invention, by applying a configuration of adding the mixture of the biocompatible macromolecular blocks, the cells, and the liquid medium to the first culture container such that the liquid surface of the mixture is over the culture surface, and stirring and culturing of the content of the first culture container after the cell structure is formed in the second culture container comprising the stirring means, it is possible to manufacture the cell structure uniformly and in large quantities for a short period of time.
(1) First Culture Container
The first culture container used in the present invention is a culture container having a culture surface on which a plurality of recessed portions are formed and a side wall part standing on an outer periphery of the culture surface.
An example of the first culture container used in the present invention will be described with reference to
In an example illustrated in
The container main body 10 has the disk-like bottom plate portion 14 and an annular side wall portion 16. The bottom plate portion 14 may be constituted with a synthesis resin material such as polystyrene or glass. For example, the bottom plate portion 14 can be manufactured through injection molding using the synthetic resin material.
The shape of the container may be a shape other than a disk shape or may be a shape such as a square. The side wall portion 16 rises from an outer peripheral edge of the bottom plate portion 14. The diameter of the bottom plate portion 14 can be set, for example, to 30 mm to 500 mm, the thickness of the bottom plate portion 14 can be set, for example, to 0.5 mm to 10 mm, and the height of the side wall portion 16 can be set, for example, to 20 mm to 100 mm, but are not particularly limited.
The lid 12 is formed in a shape corresponding to an opening portion on an upper portion of the container main body 10. The lid 12 can be used by covering the container main body 10 so as to maintain the culture environment of the cell.
As illustrated in
In the examples illustrated in
A culture surface 26 means a surface including a most upper portion of the well forming area 24 (with reference to
The depth of the recessed portion is not particularly limited, and is preferably 2 to 100 times of the size of the biocompatible macromolecular block, more preferably 2 to 10 times of the size of the biocompatible macromolecular block, and even more preferably 3 to 10 times of the size of the biocompatible macromolecular block.
The depths of the recessed portions are not particularly limited, but are preferably 10 to 2,000 μm, more preferably 20 to 1,000 μm, even more preferably 30 to 700 μm, still even more preferably 50 to 500 μm, and most preferably 100 to 400 μm.
A diameter of the recessed portion is not particularly limited, but is preferably 2 to 100 times of the size of the biocompatible macromolecular block, more preferably 3 to 50 times of the size of the biocompatible macromolecular block, and even more preferably 5 to 10 times of the size of the biocompatible macromolecular block.
The diameter of the recessed portion is not particularly limited, and is preferably 10 to 2,000 μm, more preferably 50 to 1,500 μm, even more preferably 100 to 1,500 μm, even more preferably 200 to 1,000 μm, and most preferably 400 to 1,000 μm.
It is preferable to cause the depth and the diameter of the recessed portion is in the above range, in view of having excellent performances of maintaining the strength and the shape with respect to the relationship with the size of the cell.
In a case where the recessed portion has the depth and the diameter, all of the recessed portions of the culture container are not required to have the above depth and the diameter, and at least a portion of the recessed portions may have the above depth and the above diameter.
As illustrated in
The shape (including the depth and the diameter) of the recessed portion may be uniform or may not be uniform, but is preferably uniform. The depths and the diameters of the recessed portions are preferably uniform, and it is preferable that the depths and the diameters of all of the recessed portions are substantially the same.
For example, the recessed portions 20 can be formed by irradiating the well forming area 24 with laser light. As shown in
First, a plurality of recessed portions 20 disposed in the x-axis direction are formed by emitting laser light at regular intervals (for example, 800 μm) while making an irradiation portion of a laser irradiation device to perform scanning in the positive direction of the x-axis. Subsequently, a plurality of recessed portions 20 disposed in the x-axis direction are formed by emitting laser light at regular intervals (for example, 800 μm) while the irradiation portion is made to perform scanning in the negative direction of the x-axis after the irradiation portion is made to perform scanning by a certain distance (for example, 400 μm) in the y-axis direction. Similarly, the irradiation portion is made to perform scanning by a certain distance (for example, 400 μm) in the y-axis direction. A plurality of recessed portions 20 regularly disposed on the upper surface of the bottom plate portion 14 are formed by repeating this process.
As shown in
As a laser light source, CO2 laser is used, and the laser light can be used in the pulse irradiation at an output of 10 W and an irradiation speed of 6,100 mm/min, but the present invention is not particularly limited.
Although the shapes of the irradiation spots are circular, the opening shapes of the recessed portions 20 are flattened in a substantially elliptical shape. It is considered that the flatness of the opening shapes is caused by the direction in which the synthetic resin material is poured into a metal mold during molding of the container main body 10.
In a case where the upper surface of the bottom plate portion 14 is irradiated with the laser light, the synthesis resin material constituting the bottom plate portion 14 is dissolved so as to form the recessed portions 20.
By adjusting the irradiation conditions such as the irradiation position and the output amount of the laser light, the distance between adjacent recessed portions 20, the diameters and depths of the recessed portions 20, the width and the height of the surface of the culture substrate between the recessed portions 20 adjacent to each other, and the like can be adjusted.
The well forming area 24 can be manufactured by using a die comprising protrusions forming the plurality of recessed portions 20 and recessed parts of forming the areas between recessed portions and injection molding the synthesis resin materials. The plurality of recessed portions 20 and the plurality of areas between recessed portions are formed together with the forming of the well forming area 24. In a case where the well forming area 24 is manufactured by using a die by injection molding, it is possible to form the recessed portions 20 with higher uniformity.
The area of the recessed portion is preferably 70% or more, more preferably 80% or more, even more preferably 90% or more, and most preferably 100% with respect to the total area of the culture surface. It is preferable to set the ratio of the area of the recessed portions to be within the above-described range from the viewpoint of the effect of the present invention.
The area of the recessed portions means the area in a case where the recessed portions are two-dimensionally caught in a case where the recessed portions are observed from above, and means the area of the region defined by the diameter of the recessed portion described above in the present specification. As illustrated in
Two recessed portions 20 adjacent to each other are formed via an area between the recessed portions. The surface of the culture substrate between the mutually adjacent recessed portions 20 may be flat or non-flat, but is preferably non-flat.
It is preferable that a treatment of suppressing cell adhesion is performed on the culture surface and the surface of the recessed portion. Accordingly, after the cell structure is cultured, the cell structure can be easily peeled off. Examples of the treatment of suppressing the cell adhesion include coating with a cell adhesion suppressant (see
(2) Biocompatible Macromolecular Block
(2-1) Biocompatible Macromolecules
Biocompatibility means a property which does not cause a significantly harmful reaction such as a long-term and chronic inflammatory reaction, during contact with a living body. Whether or not the biocompatible macromolecules used in the present invention are decomposed within a living body is not particularly limited as long as the biocompatible macromolecules have affinity to the living body. However, biodegradable macromolecules are preferable. Specific examples of non-biodegradable materials include polytetrafluoroethylene (PTFE), polyurethane, polypropylene, polyester, vinyl chloride, polycarbonate, acryl, stainless steel, titanium, silicone, and 2-methacryloyloxyethyl phosphorylcholine (MPC). Specific examples of the biodegradable material include a polypeptide (for example, gelatin described below) such as a naturally occurring peptide, a recombinant peptide, or a chemically synthesized peptide, polylactic acid, polyglycolic acid, a lactic acid/glycolic acid copolymer (PLGA), hyaluronic acid, glycosaminoglycan, proteoglycan, chondroitin, cellulose, agarose, carboxymethyl cellulose, chitin, and chitosan. Among these, a recombinant peptide is particularly preferable. Devising of an improvement of cell adhesion properties in these biocompatible macromolecules may be performed. Specifically, methods such as “Coating substrate surface with cell adhesion base material (fibronectin, vitronectin, and laminin) or a cell adhesion sequence (RGD sequence, LDV sequence, REDV sequence (SEQ ID NO: 2), YIGSR sequence (SEQ ID NO: 3), PDSGR sequence (SEQ ID NO: 4), RYVVLPR sequence (SEQ ID NO: 5), LGTIPG sequence (SEQ ID NO: 6), RNIAEIIKDI sequence (SEQ ID NO: 7), IKVAV sequence (SEQ ID NO: 8), LRE sequence, DGEA sequence (SEQ ID NO: 9), and HAV sequence, expressed as a single amino acid symbol)”, “Amination and cationization of substrate surface”, or “Plasma treatment of substrate surface and hydrophilic treatment by corona discharge” can be used.
The kinds of polypeptide including a recombinant peptide or a chemically synthesized peptide is not particularly limited, as long as the polypeptide has biocompatibility, but, for example, gelatin, collagen, elastin, fibronectin, pronectin, laminin, tenascin, fibrin, fibroin, entactin, thrombo spondin, and retronectin are preferable, and gelatin, collagen, and atelocollagen are most preferable. Gelatin for use in the present invention is preferably natural gelatin, recombinant gelatin, or chemically synthesized gelatin and more preferably recombinant gelatin. The natural gelatin referred to herein means gelatin manufactured using naturally derived collagen.
A chemically synthesized peptide or chemically synthesized gelatin means an artificially synthesized peptide or gelatin. The synthesis of a peptide such as gelatin may be solid phase synthesis or liquid phase synthesis, but is preferably solid phase synthesis. The solid phase synthesis of a peptide is well-known to those skilled in the art, and examples thereof include a fluorenyl-methoxy-carbonyl group (Fmoc group) synthesis method in which a Fmoc group is used for protection of an amino group, and a tert-butyl oxy carbonyl group (Boc group) synthesis method in which a Boc group is used for protection of an amino group. The contents described in (2-3) Gelatin below in the present specification can be applied to the preferable embodiments of the chemically synthesized gelatin.
Gelatin, particularly recombinant gelatin, is described below in the present specification.
A “1/IOB” value which is a hydrophilicity value of the biocompatible polymer used in the present invention is preferably 0 to 1.0. The value is more preferably within a range of 0 to 0.6, and even more preferably within a range of 0 to 0.4. IOB is an index of hydrophilic and hydrophobic properties based on an organic conceptual diagram representing polarity and non-polarity of an organic compound proposed by Atsushi HUJITA, and the details thereof are described in, for example, “Pharmaceutical Bulletin”, vol. 2, 2, pp. 163-173 (1954), “Area of Chemistry” vol. 11, 10, pp. 719-725 (1957), and “Fragrance Journal, vol. 50, pp. 79-82 (1981). Briefly, the root of every organic compound is set to methane (CH4), and all of other compounds are regarded as derivatives of methane. Certain numerical values for the number of carbons thereof, a substituent group, a transformation portion, a ring, and the like are set, and an organic value (OV) and an inorganic value (IV) are obtained by adding the score thereof. These values are plotted on a diagram in which the organic value is represented on the X-axis and the inorganic value is represented on the Y-axis. IOB in the organic conceptual diagram refers to a ratio of the inorganic value (IV) to the organic value (OV) in the organic conceptual diagram, that is, “inorganic value (IV)/organic value (OV)”. The details of the organic conceptual diagram can be referred to “New Edition Organic Conceptual Diagram—Foundation and Application-” (written by Yoshio KOUDA, Sankyo Shuppan Co., Ltd., 2008). In the present specification, the hydrophilic and hydrophobic properties are represented by a “1/IOB” value which was obtained by taking a reciprocal number of JOB. This is a notation of representing more hydrophilic properties as the “1/IOB” value becomes small (close to 0).
In a case where the “1/IOB” value of the polymer used in the present invention is caused to be in the above range, hydrophilic properties become high, and water absorption properties become high, so as to effectively act on retention of nutritional components.
In a case where the biocompatible macromolecules used in the present invention are polypeptides, the hydrophilic and hydrophobic indexes represented by a grand average of hydropathicity (GRAVY) value are preferably −9.0 to 0.3, and more preferably −7.0 to 0.0. The grand average of hydropathicity (GRAVY) value can be obtained by methods of “Gasteiger E., Hoogland C., Gattiker A., Duvaud S., Wilkins M. R., Appel R. D., Bairoch A.; Protein Identification and Analysis Tools on the ExPASy Server; (In) John M. Walker (ed): The Proteomics Protocols Handbook, Humana Press (2005). pp. 571-607” and “Gasteiger E., Gattiker A., Hoogland C., Ivanyi I., Appeal R. D., Bairoch A.; ExPASy: the proteomics server for in-depth protein knowledge and analysis.; Nucleic Acids Res. 31:3784-3788 (2003)”.
The hydrophilic properties and water absorbency become high by making the GRAVY value of the macromolecules used in the present invention be within the above-described range, which effectively acts to hold nutrient components.
(2-2) Cross-Linking
The biocompatible macromolecules used in the present invention may be or may not be cross-linked, but are preferably cross-linked. By using the cross-linked biocompatible macromolecules, it is possible to obtain an effect of preventing instant decomposition during culturing in a medium and during transplantation into a living body. As general cross-linking methods, thermal cross-linking, cross-linking using aldehydes (for example, formaldehyde or glutaraldehyde), cross-linking using a condensation agent (carbodiimide, cyanamide, or the like), enzymatic cross-linking, photocrosslinking, ultraviolet cross-linking, a hydrophobic interaction, hydrogen bonding, an ionic interaction, and the like are known, it is also possible to use the above-described cross-linking methods in the present invention. As the cross-linking methods used in the present invention, thermal cross-linking, ultraviolet cross-linking, or enzymatic cross-linking is more preferable, and thermal cross-linking is particularly preferable.
In a case where crosslinking by an enzyme is performed, the enzyme is not particularly limited, as long as the enzyme has a crosslinking action between macromolecular materials, but crosslinking can be performed preferably by using transglutaminase and laccase and most preferably by using transglutaminase. Specific examples of protein to be subjected to enzymatic cross-linking using transglutaminase are not particularly limited as long as the protein has a lysine residue and a glutamine residue. The transglutaminase may be derived from a mammal or a microorganism, and specific examples thereof include ACTIVA series manufactured by Ajinomoto Co., Inc., mammal-derived transglutaminase commercially available as a reagent, such as guinea pig liver-derived transglutaminase, goat-derived transglutaminase, and rabbit-derived transglutaminase manufactured by Oriental Yeast Co., Ltd., The Meridian Life Science, Inc., and the like, and human-derived blood coagulation factors (Factor XIIIa, Haematologic Technologies, Inc.).
The reaction temperature in a case of performing cross-linking (for example, thermal cross-linking) is not particularly limited as long as cross-linking can be performed, but is preferably −100° C. to 500° C., more preferably 0° C. to 300° C., even more preferably 50° C. to 300° C., still even more preferably 100° C. to 250° C., and still even more preferably 120° C. to 200° C.
(2-3) Gelatin
The biocompatible macromolecules are preferably gelatin. The gelatin may be any of natural gelatin, recombinant gelatin, or chemically synthesized gelatin.
The recombinant gelatin referred in the present invention means polypeptides or protein-like substances which have an amino acid sequence similar to that of gelatin manufactured through gene recombination technology. The gelatin which can be used in the present invention preferably has a repeat of the sequence represented by Gly-X-Y specific to collagen (X and Y each independently represent any amino acid). Here, a plurality of Gly-X-Y's may be identical to or different from each other. Preferably, two or more sequences of cell adhesion signals are included in one molecule. As gelatin used in the present invention, gelatin having an amino acid sequence derived from a partial amino acid sequence of collagen can be used. Recombinant gelatins disclosed in, for example, EP1014176, U.S. Pat. No. 6,992,172B, WO2004/085473A, and WO2008/103041A can be used. However, the recombinant gelatin is not limited thereto. The gelatin used in the present invention is preferably gelatin according to an aspect below.
The recombinant gelatin is excellent in biocompatibility with original performance of natural gelatin, and is excellent in non-infection properties since there is no concern of bovine spongiform encephalopathy (BSE) and the recombinant gelatin with not being naturally derived. The recombinant gelatin is even compared to natural gelatin, and a sequence is determined. Therefore, it is possible to accurately design the strength and degradability so as to reduce deviation through cross-linking or the like.
The molecular weight of the gelatin is not particularly limited, but is preferably 2,000 to 100,000 (2 kDa to 100 kDa), more preferably 2,500 to 95,000 (2.5 kDa to 95 kDa), even more preferably 5,000 to 90,000 (5 kDa to 90 kDa), and most preferably 10,000 to 90,000 (10 kDa to 90 kDa).
The gelatin preferably has a repeat of the sequence represented by Gly-X-Y specific to collagen. Here, a plurality of Gly-X-Y's may be identical to or different from each other. In Gly-X-Y, Gly represents glycine and X and Y represent any amino acid (preferably represents any amino acid other than glycine). The sequence represented by Gly-X-Y characteristic to collagen is a partial structure which is extremely specific compared to other protein in a composition or a sequence of an amino acid of gelatin/collagen. In this section, glycine occupies about one-third of the entirety of the amino acid sequence, one sequence is repeated every three sequences. Glycine is the simplest amino acid. Therefore, there is a little restraint in disposition of molecular chains and glycine significantly contributes to regeneration of a helix structure during gelation. The amino acid represented by X and Y include a large amount of imino acid (proline and oxyproline), and preferably occupies 10% to 45% with respect to the total. Preferably 80% or more, more preferably 95% or more, and most preferably 99% or more of the amino acid of the gelatin sequence have the repeating structure of Gly-X-Y.
In general gelatin, a polar amino acid with an electrical charge and a polar non-charged amino acid exist by 1:1 in polar amino acids. Here, the polar amino acid specifically indicates cysteine, aspartic acid, glutamic acid, histidine, lysine, asparagine, glutamine, serine, threonine, tyrosine, or arginine. Among these, the polar non-charged amino acid indicates cysteine, asparagine, glutamine, serine, threonine, or tyrosine. In the gelatin used in the present invention, the proportion of the polar amino acids is 10% to 40% and preferably 20% to 30% with respect to the total constituting amino acid. It is preferable that the proportion of a non-charged amino acid in the polar amino acid is greater than or equal to 5% and less than 20% and preferably less than 10%. It is preferable not to include any one amino acid of serine, threonine, asparagine, tyrosine, or cysteine, preferably two or more of the amino acids in the sequence.
In general, in polypeptides, minimum amino acid sequences which work as cell adhesion signals are known (for example, Nagai Shoten Co., Ltd., “Pathophysiology”, Vol. 9, No. 7 (1990) p. 527). The gelatin used in the present invention preferably has two or more of these cell adhesion signals in one molecule. As the specific sequences, sequences such as an RGD sequence, an LDV sequence, an REDV sequence (SEQ ID NO: 2), a YIGSR sequence (SEQ ID NO: 3), a PDSGR sequence (SEQ ID NO: 4), an RYVVLPR sequence (SEQ ID NO: 5), an LGTIPG sequence (SEQ ID NO: 6), an RNIAEIIKDI sequence (SEQ ID NO: 7), an IKVAV sequence (SEQ ID NO: 8), an LRE sequence, a DGEA sequence (SEQ ID NO: 9), and an HAV sequence, which are represented by one-letter notation of amino acids are preferable in that there are many kinds of cells adhered. An RGD sequence, a YIGSR sequence (SEQ ID NO: 3), a PDSGR sequence (SEQ ID NO: 4), an LGTIPG sequence (SEQ ID NO: 6), an IKVAV sequence (SEQ ID NO: 8), and a HAV sequence are more preferable and an RGD sequence is particularly preferable. In the RGD sequence, an ERGD sequence (SEQ ID NO: 10) is preferable. By using gelatin having a cell adhesion signal, the amount of base material production of cells can be improved. For example, it is possible to improve the manufacturing of glycosaminoglycan (GAG) in a case of cartilage differentiation using mesenchymal stem cells as cells.
As the arrangement of RGD sequences in gelatin used in the present invention, the number of amino acids between RGDs is not uniform between 0 and 100 and preferably between 25 and 60.
The content of this minimum amino acid sequence is preferably 3 to 50, more preferably 4 to 30, and particularly preferably 5 to 20 in one molecule of protein in view of cell adhesion properties and proliferation properties. The most preferable content thereof is 12.
In the gelatin used in the present invention, the ratio of the RGD motif to the total number of amino acids is preferably at least 0.4%. In a case where the gelatin includes more than 350 amino acids, it is preferable that each stretch of 350 amino acids includes at least one RGD motif. The proportion of RGD motifs with respect to the total number of amino acids is even more preferably at least 0.6%, still even more preferably at least 0.8%, still even more preferably at least 1.0%, still even more preferably at least 1.2%, and most preferably at least 1.5%. The number of RGD motifs in the peptide is preferably at least 4, more preferably at least 6, more preferably at least 8, more preferably 12 or more and 16 or less per 250 amino acids. The proportion of RGD motifs being 0.4% corresponds to at least one RGD sequence per 250 amino acids. Since the number of RGD motifs is an integer, in order to satisfy the characteristics of at least 0.4%, gelatin including 251 amino acids is required to include at least two RGD sequences. The gelatin according to the embodiment of the present invention preferably includes at least 2 RGD sequences per 250 amino acids, more preferably at least 3 RGD sequences per 250 amino acids, and more preferably at least 4 RGDs per 250 amino acids. The gelatin according to another embodiment of the present invention includes at least 4 RGD motifs, preferably includes at least 6 RGD motifs, more preferably at least 8 RGD motifs, and even more preferably includes 12 to 16 RGD motifs.
The gelatin may be partially hydrolyzed.
It is preferable that the gelatin used in the present invention is represented by Formula 1: A-[(Gly-X-Y)n]m-B. n X's each independently represent any amino acid and n Y's each independently represent any amino acid. m preferably represents an integer of 2 to 10 and more preferably represents an integer of 3 to 5. n is preferably an integer of 3 to 100, more preferably an integer of 15 to 70, and most preferably an integer of 50 to 65. A represents any amino acid or an amino acid sequence, B represents any amino acid or an amino acid sequence. n Gly-X-Y's may be identical to or different from each other.
It is more preferable that the gelatin used in the present invention is represented by Formula: Gly-Ala-Pro-[(Gly-X-Y)63]3-Gly (SEQ ID NO: 11) (in the formula, 63 X's (=Xaa) each independently represent any of the amino acids, and 63 Y's (=Xaa) independently represent any of the amino acids. 63 Gly-X-Y's may be identical to or different from each other).
It is preferable that a plurality of sequence units of collagen which naturally exists are bonded to a repeating unit. Any naturally existing collagen referred to herein may be used as long as the collagen naturally exists, but is preferably I type collagen, II type collagen, III type collagen, IV type collagen, or V type collagen, and more preferably I type collagen, II type collagen, or III type collagen. According to another form, the above-described collagen is preferably derived from a human-type, cattle, a pig, a mouse, or a rat, and is more preferably derived from a human-type.
The isoelectric point of the gelatin used in the present invention is preferably 5 to 10, more preferably 6 to 10, and even more preferably 7 to 9.5. The isoelectric point of the gelatin is measured by measuring pH after a 1 mass % gelatin solution is caused to pass through the mixed crystal column of an exchange resin by an isoelectric focusing method (see Maxey, C. R. (1976; Phitogr. Gelatin 2, Editor Cox, P. J. Academic, London, Engl.).
It is preferable that the gelatin is not deaminated.
It is preferable that the gelatin does not have telopentide.
It is preferable that the gelatin is a substantially pure polypeptide prepared by a nucleic acid coding an amino acid sequence.
The gelatin used in the present invention is particularly preferably
(1) a peptide formed of an amino acid sequence described in SEQ ID No: 1;
(2) a peptide which is formed of an amino acid sequence in which one or several amino acids are deleted, substituted, or added in the amino acid sequence described in SEQ ID No: 1, and has biocompatibility; or
(3) a peptide which is formed of an amino acid sequence having 80% or more (more preferably 90% or more, particularly preferably 95% or more, and most preferably 98% or more) sequence identity to the amino acid sequence described in SEQ ID No: 1, and has biocompatibility.
“One or several” in the expression “amino acid sequence in which one or several amino acids are deleted, substituted, or added” preferably means 1 to 20 amino acids, more preferably means 1 to 10 amino acids, even more preferably means 1 to 5 amino acids, and particularly preferably means 1 to 3 amino acids.
The recombinant gelatin used in the present invention can be manufactured through gene recombination technology which is known to those skilled in the art, and can be manufactured in accordance with, for example, methods disclosed in EP1014176A2, U.S. Pat. No. 6,992,172B, WO2004/085473A, and WO2008/103041A. Specifically, a gene encoding an amino acid sequence of predetermined recombinant gelatin is acquired, the acquired gene is incorporated into an expression vector to manufacture a recombinant expression vector, and a transformant is manufactured by introducing the recombinant expression vector into an appropriate host. The recombinant gelatin is manufactured by culturing the obtained transformant in an appropriate medium. Therefore, it is possible to prepare the gelatin used in the present invention by collecting the recombinant gelatin manufactured from a culture product.
(2-4) Biocompatible Macromolecular Block
In the present invention, a block (aggregation) formed of the above-described biocompatible macromolecules is used.
The shape of the biocompatible macromolecular block according to the embodiment of the present invention is not particularly limited. Examples thereof include an amorphous shape, a spherical shape, a particulate shape (granule), a powdery shape, a porous shape, a fibrous shape, a spindle shape, a flat shape, and a sheet shape. An amorphous shape, a spherical shape, a particulate shape (granule), a powdery shape, and a porous shape are preferable. The amorphous shape indicates that the shape of a surface is uneven, and indicates, for example, an object, such as rock, which has roughness. Examples of the above-described shapes are not distinct from each other. For example, in some cases, an example of a subordinate concept of the particulate shape (granule) is an amorphous shape.
The shape of the biocompatible macromolecular block according to the embodiment of the present invention is not particularly limited as described above. However, the tap density is preferably 10 mg/cm3 to 500 mg/cm3, more preferably 20 mg/cm3 to 400 mg/cm3, even more preferably 40 mg/cm3 to 220 mg/cm3, and particularly preferably 50 mg/cm3 to 150 mg/cm3.
The tap density is a value indicating how much volume of block can be densely filled. It can be seen that, as the value becomes smaller, the block cannot be densely filled, that is, the structure of the block is complicated. It is considered that the tap density of the biocompatible macromolecular block indicates the complexity of a surface structure of the biocompatible macromolecular block and the amount of void formed in a case where biocompatible macromolecular blocks are collected as an aggregate. As the tap density becomes smaller, the void between biocompatible macromolecular blocks becomes larger and a grafted region of a cell becomes larger. In addition, in a case where the tap density is not too small, the biocompatible macromolecular block can appropriately exist between cells and nutrients can be delivered into a cell structure in a case where the cell structure is manufactured, and therefore, it is considered that it is preferable that the tap density falls within the above-described range.
The tap density referred to in the present specification can be measured as follows. A container (with a cylindrical shape with a diameter of 6 mm and a length of 21.8 mm: a capacity of 0.616 cm3) (hereinafter, described as a cap) is prepared for the measurement of the tap density. First, the mass of only a cap is measured. Thereafter, a funnel is attached to the cap, and blocks are poured from the funnel so as to be collected in the cap. After placing a sufficient amount of block, the cap portion is hit 200 times on a hard object such as a desk, the funnel is removed, and the blocks are leveled with a spatula. The mass is measured in a state where the cap is filled up with the blocks. The tap density can be obtained by calculating the mass of only the blocks from the difference between the mass of the cap filled up with the blocks and the mass of only the cap, and dividing the mass of only the blocks by the volume of the cap.
The cross-linking degree of the biocompatible macromolecular block according to the embodiment of the present invention is not particularly limited, but is preferably greater than or equal to 2, more preferably 2 to 30, even more preferably 4 to 25, and particularly preferably 4 to 22.
The method for measuring the solid (the number of cross-linking times per molecule) of a biocompatible macromolecular block is not particularly limited. However, the cross-linking degree can be measured, for example, through a TNBS (2,4,6-trinitrobenzene sulfonic acid) method in examples to be described below. Specifically, a sample obtained by mixing biocompatible macromolecular blocks, a NaHCO3 aqueous solution, and a TNBS aqueous solution, allowing the mixture to react for 3 hours at 37° C., and then, stopping the reaction, and a blank obtained by mixing biocompatible macromolecular blocks, a NaHCO3 aqueous solution, and a TNBS aqueous solution and stopping a reaction immediately after the mixing were prepared. The cross-linking degree (the number of cross-linking times per molecule) can be calculated from (Formula 2) and (Formula 3) by measuring each absorbance (345 nm) of the sample and the blank which have been diluted with pure water.
(As−Ab)/14,600×V/w (Formula 2)
(Formula 2) represents the amount (molar equivalent) of lysine per 1 g of biocompatible macromolecular blocks.
(in the formula, As represents the sample absorbance, Ab represents the blank absorbance, V represents the amount (g) reaction liquid, and w represents the mass (mg) of the biocompatible macromolecular blocks.)
1−(sample (Formula 2)/uncross-linked macromolecules (Formula 2))×34 (Formula 3)
(Formula 3) represents the number of cross-linking times per molecule.
The water absorption rate of the biocompatible macromolecular block according to the embodiment of the present invention is not particularly limited, but is preferably greater than or equal to 300%, more preferably greater than or equal to 400%, even more preferably greater than or equal to 500%, particularly preferably greater than or equal to 700%, and most preferably greater than or equal to 800%. The upper limit of the water absorption rate is not particularly limited, but is generally less than or equal to 4,000% or less than or equal to 2,000%.
The method for measuring the water absorption rate of the biocompatible macromolecular block is not particularly limited. However, the water absorption rate of the biocompatible macromolecular block can be measured, for example, through the method in examples to be described below. Specifically, a 3 cm×3 cm nylon mesh bag is filled with about 15 mg of biocompatible macromolecular blocks at 25° C. and is swollen in ion exchange water for 2 hours. Then, the biocompatible macromolecular blocks are dried with air for 10 minutes, and the mass is measured at each stage to obtain the water absorption rate according to (Formula 4).
Water absorption rate=(w2−w1−w0)/w0 (Formula 4)
(in the formula, w0 represents the mass of a material before water absorption, w1 represents the mass of an empty bag after water absorption, and w2 represents the mass of the entirety of the bag containing the material after water absorption.)
The size of one biocompatible macromolecular block according to the embodiment of the present invention is not particularly limited, but is preferably 1 μm to 700 μm, more preferably 10 μm to 700 μm, even more preferably 10 μm to 300 μm, still even more preferably 20 μm to 200 μm, still even more preferably 20 μm to 150 μm, and particularly preferably 53 μm to 106 μm. It is possible to favorably deliver nutrients into a cell structure from the outside by setting the size of one biocompatible macromolecular block to be within the above-described range. The size of one biocompatible macromolecular block does not mean that an average value of the sizes of a plurality of biocompatible macromolecular blocks is within the above-described range, but means the size of each biocompatible macromolecular block which is obtained by sieving a plurality of biocompatible macromolecular blocks.
The size of one block can be defined by the size of a sieve used in a case of dividing the block. For example, blocks remaining on a sieve with 106 μm in a case where blocks which have been passed through a sieve with 180 μm for sifting are sifted using the sieve with 106 μm can be regarded as blocks having a size of 106 to 180 μm. Next, blocks remaining on a sieve with 53 μm in a case where blocks which have been passed through the sieve with 106 μm for sifting are sifted using the sieve with 53 μm can be regarded as blocks having a size of 53 to 106 μm. Next, blocks remaining on a sieve with 25 μm in a case where blocks which have been passed through the sieve with 53 μm for sifting are sifted using the sieve with 25 μm can be regarded as blocks having a size of 25 to 53 μm.
(2-5) Method for Manufacturing Biocompatible Macromolecular Block
The method for manufacturing a biocompatible macromolecular block is not particularly limited. For example, it is possible to obtain a biocompatible macromolecular block by pulverizing a solid matter (such as a porous body of a biocompatible macromolecule) containing a biocompatible macromolecule using a pulverizer (such as NEW POWERMILL). The solid matter (such as a porous body of a biocompatible macromolecule) containing a biocompatible macromolecule can be obtained, for example, by freeze-drying an aqueous solution containing the biocompatible macromolecule.
It is possible to produce an amorphous biocompatible macromolecular block of which the shape of the surface is uneven, by pulverizing a solid matter containing a biocompatible macromolecule as described above.
An example of the method for manufacturing a porous body of a biocompatible macromolecule include a method including
(a) a step of cooling a solution of biocompatible macromolecules under the conditions where the difference between the temperature of a portion having the highest liquid temperature within the solution and the temperature of a portion having the lowest liquid temperature within the solution is lower than or equal to 2.5° C. and the temperature of a portion having the highest liquid temperature within the solution is lower than or equal to a melting point, to an unfrozen state,
(b) a step of freezing the solution of the biocompatible macromolecules obtained in the step (a), and
(c) a step of freeze-drying the frozen biocompatible macromolecules obtained in the step (b).
In a case where the solution of the biocompatible macromolecules is cooled to an unfrozen state, the variation in the size of obtained porous pores is reduced by making the difference between the temperature of a portion having the highest liquid temperature in the solution and the temperature of a portion having the lowest liquid temperature in the solution be lower than or equal to 2.5° C. (preferably lower than or equal to 2.3° C. and more preferably lower than or equal to 2.1° C.), that is, by reducing the difference in temperature. The lower limit of the difference between the temperature of a portion having the highest liquid temperature in the solution and the temperature of a portion having the lowest liquid temperature in the solution is not particularly limited, but may be higher than or equal to 0° C. For example, the lower limit thereof may be higher than or equal to 0.1° C., higher than or equal to 0.5° C., higher than or equal to 0.8° C., or higher than or equal to 0.9° C.
The cooling in the step (a) is preferably carried out, for example, using a material (preferably TEFLON (registered trademark)) having a lower thermal conductivity than water. The portion having the highest liquid temperature within the solution can be supposed as the farthest portion from a cooling side, and the portion having the lowest liquid temperature within the solution can be supposed as a liquid temperature of the cooled surface.
In the step (a), the difference between the temperature of a portion having the highest liquid temperature within the solution and the temperature of a portion having the lowest liquid temperature within the solution immediately before generation of solidification heat is preferably lower than or equal to 2.5° C., more preferably lower than or equal to 2.3° C., and even more preferably lower than or equal to 2.1° C. Here, the “difference in temperature immediately before the generation of solidification heat” means a difference in temperature in a case where the difference in temperature becomes largest between 1 second and 10 seconds before the generation of solidification heat.
In the step (a), the temperature of a portion having the lowest liquid temperature within the solution is preferably lower than or equal to a melting point of a solvent −5° C., more preferably lower than or equal to a melting point of a solvent −5° C. and higher than or equal to a melting point of a solvent −20° C., and even more preferably lower than or equal to a melting point of a solvent −6° C. and higher than or equal to a melting point of a solvent −16° C. The solvent of a melting point of a solvent is a solvent of a solution of biocompatible macromolecules.
In the step (b), the solution of the biocompatible macromolecules obtained in the step (a) is frozen. The cooling temperature for the freezing in the step (b) is not particularly limited. Depending on cooling equipment, the cooling temperature is preferably a temperature which is 3° C. to 30° C. lower than the temperature of a portion having the lowest liquid temperature within the solution, more preferably a temperature which is 5° C. to 25° C. lower than the temperature of a portion having the lowest liquid temperature within the solution, and even more preferably a temperature which is 10° C. to 20° C. lower than the temperature of a portion having the lowest liquid temperature within the solution.
In the step (c), the frozen biocompatible macromolecules obtained in the step (b) are freeze-dried. The freeze-drying can be performed through a usual method. For example, the freeze-drying can be performed by carrying out vacuum drying at a temperature lower than a melting point of a solvent and further carrying out vacuum drying at room temperature (20° C.).
In the present invention, a biocompatible macromolecular block can be preferably manufactured by pulverizing the porous body obtained in the above-described step (c).
(3) Cell
Any cells can be used as the cells used in the present invention as long as it is possible to perform cell transplantation which is the object of the cell structure according to the embodiment of the present invention, and the types thereof are not particularly limited. In addition, one type of cell may be used, or a plurality of types of cells may be used in combination. In addition, cells to be used are preferably animal cells, more preferably vertebrate-derived cells, and particularly preferably human-derived cells. The types of vertebrate-derived cells (particularly, human-type-derived cells) may be any of universal cells, somatic stem cells, precursor cells, and mature cells. It is possible to use, for example, embryonic stem (ES) cells, germ-stem (GS) cells, or artificial pluripotent stem (iPS) cells as the universal cells. It is possible to use, for example, mesenchymal stem cells (MSC), hematopoietic stem cells, amniotic cells, umbilical cord blood cells, bone marrow-derived cells, myocardial stem cells, adipose-derived stem cells, or neural stem cells can be used as the somatic stem cell. It is possible to use, for example, skin, dermis, epidermis, muscle, cardiac muscles, nerves, bones, cartilage, endothelium, brain, epithelium, heart, kidney, liver, pancreas, spleen, oral cavity, cornea, bone marrow, umbilical cord blood, amnion, or cells derived from hair as the precursor cells and the mature cells. It is possible to use, for example, ES cells, iPS cells, MSCs, chondrocytes, osteoblasts, osteoprecursor cells, mesenchymal cells, myoblasts, cardiac muscle cells, cardiomyoblasts, nerve cells, hepatocytes, beta cells, fibroblasts, corneal endothelial cells, vascular endothelial cells, corneal epithelial cells, amniotic cells, umbilical cord blood cells, bone marrow derived cells, or hematopoietic stem cells as the human-type derived cells. The cells may be derived from any of autologous cells and heterologous cells.
For example, it is possible to suitably use, for example, cardiac muscle cells, smooth muscle cells, fibroblasts, skeletal muscle-derived cells (particularly satellite cells), and bone marrow cells (particularly, bone marrow cells differentiated into myocardial-like cells) which are autologous and have been extracted from heterologous cells, in heart diseases such as severe heart failure and severe myocardial infarction. Furthermore, cells for transplantation can be appropriately selected in other organs. Examples of the transplantation include transplantation of neural precursor cells or cells capable of being differentiated into nerve cells into cerebral ischemia or cerebral infarction sites, and transplantation of vascular endothelial cells or cells capable of being differentiated into vascular endothelial cells into myocardial infarction or skeletal muscle ischemia sites.
In addition, examples of the cells to be used for cell transplantation include cells to be used for cell transplantation for diabetic organ disorders. For example, there are cells for cell transplantation therapy in which diseases such as blood circulation disorders in the kidney, the pancreas, peripheral nerves, the eyes, and the limbs are intensively studied. That is, attempts to transplant insulin-secreting cells into the pancreas with a decreased insulin secretion ability, transplantation of bone marrow-derived cells into limbs with circulatory disorders, and the like are have been studied, and such cells can be used.
In the present invention, vascular cells can also be used. In the present specification, the vascular cells mean cells associated with angiogenesis, and are cells forming blood vessels and blood or precursor cells capable of being differentiated into the cells, or somatic stem cells. Here, cells such as mesenchymal stem cells (MSC) or universal cells such as ES cells, GS cells, or iPS cells, which are not naturally differentiated into cells forming blood vessels and blood are not included in the vascular cells. The vascular cells are preferably cells forming a blood vessel. In vertebrate-derived cells (particularly, human-derived cells), specific examples of the cells forming blood vessels include vascular endothelial cells and vascular smooth muscle cells. The vascular endothelial cells may be either venous endothelial cells or arterial endothelial cells. Vascular endothelial precursor cells can be used as precursor cells of the vascular endothelial cells. Vascular endothelial cells and vascular endothelial precursor cells are preferably used. Blood cells can be used as the cells forming blood. It is possible to use white blood cells such as lymphocytes or neutrophils, monocyte cells, and hematopoietic stem cells which are stem cells thereof.
In the present specification, non-vascular cells mean cells other than the above-described vascular cells. For example, ES cells, iPS cells, mesenchymal stem cells (MSC), myocardial stem cells, cardiac muscle cells, fibroblasts, myoblasts, chondrocytes, myoblasts, hepatocytes or nerve cells can be used. MSC, chondrocytes, myoblasts, myocardial stem cells, cardiac muscle cells, hepatocytes, or iPS cells can be preferably used. MSC, myocardial stem cells, cardiac muscle cells, or myoblasts can be more preferably used.
(4) Method for Manufacturing Cell Structure
In the step (A) of the method of manufacturing a cell structure according to the embodiment of the present invention, the mixture of the biocompatible macromolecular blocks, the cells, and the liquid medium is added to the first culture container having the culture surface on which the plurality of recessed portions are formed and the side wall part standing on the outer periphery of the culture surface, such that the liquid surface of the mixture is over the culture surface.
The kind of the liquid medium is not particularly limited, and can be appropriately selected according to the kinds of the used cells, but for example, the liquid medium may be a growth medium or a differentiation medium.
Examples of the proliferation medium include Dulbecco's Modified Eagle Medium (DMEM)+10% fetal bovine serum (FBS), MSCGM BulletKit (trademark) of Takara Bio Inc. and an EGM-2+ECFC serum supplement of Lonza, but is not particularly limited.
Examples of the differentiation medium include a mesenchymal stem cell chondrocyte differentiation medium (Mesenchymal Stem Cell Chondrogenic Differentiation Medium) of Takara Bio Inc., a mesenchymal stem cell osteoblast differentiation medium (Mesenchymal Stem Cell Osteogenic Differentiation Medium) of Takara Bio Inc., but is not particularly limited.
In the step (B) of the method of manufacturing a cell structure according to the embodiment of the present invention, a cell structure in which the first culture vessel of the step (A) is allowed to stand, biocompatible macromolecular blocks and cells are included in the recessed portion, and the plurality of biocompatible macromolecular blocks are disposed in gaps between the plurality of cells is formed.
In the step (B), the first culture container is allowed to stand until the free biocompatible macromolecular blocks are preferably 30 mass % or less (more preferably 10 mass % or less, even more preferably 5 mass % or less, and most preferably 0 mass %) with respect to the total biocompatible macromolecular blocks. A case where “the free biocompatible macromolecular block is 0 mass % of the total biocompatible macromolecular block” is a case where a free biocompatible macromolecular block is not present.
It is preferable that the first culture container is allowed to stand in the step (B) for a period of time for which the ratio of the number of cell structures manufactured after the step (C) to the number of recessed portions is 70% or more.
In the step (B), the period of time for allowing the first culture container to stand is preferably 2 hours to 24 hours and more preferably 3 hours to 16 hours. In a case where the standing time is 2 or more hours, the adhesion between the biocompatible macromolecular block and the cell becomes satisfactory, and thus in a case of being provided in the stirring culture step, the separation between the biocompatible macromolecular block and the cell can be suppressed, such that the cell structure can be effectively formed. In a case where the standing time is 24 hours or less, the fusion of cell structures can be suppressed, and thus a large number of uniform cell structures can be obtained.
The step (B) can be performed in a CO2 incubator as desired, and is performed generally at 30° C. to 45° C. and preferably 35° C. to 40° C. (for example, 37° C.).
In the step (C) of the method of manufacturing the cell structure according to the embodiment of the present invention, the content of the first culture container obtained in the step (B) is stirred and cultured in the second culture container comprising the stirring means.
The content of the first culture container includes a liquid medium, a cell structure, a biocompatible macromolecular block not forming the cell structure, and a cell not forming the cell structure.
An operation of transferring the content of the first culture container obtained in the step (B) to a second culture container comprising the stirring means is not particularly limited, but can be performed by a general method, and for example, the content of the first culture container can be transferred to a second culture container comprising stirring means by using a pippet.
The second culture container is a container of stirring and culturing and comprises stirring means. As the stirring means, a stirring blade, a stirrer, or means for rotating or vibrating the container can be used. As the second culture container, a commercially available culture container (for example, a product name of 30 mL single use bioreactor (BWV-S03A manufactured by ABLE Corporation)) can also be used.
As the medium used in the stirring and culturing in the step (C), the same medium as the liquid medium described in the step (A) can be used. The medium used in the stirring and culturing in the step (C) may be the same medium as the liquid medium used in the step (A) or may be a different medium, but is preferably the same medium. In a case where the medium used in the step (C) is the same liquid medium used in the step (A), in the step (C), stirring and culturing may be performed after the medium is changed into a new medium.
The period of time for stirring and culturing the content of the first culture container in the step (C) is preferably 12 hours to 93 hours and more preferably 18 hours to 48 hours. In a case where stirring and culturing may be performed for the above period of time, cell structures having uniform ratios, shapes, and sizes of the macromolecular blocks having biocompatibility and the cells can be easily manufactured.
The stirring speed in the stirring and culturing is preferably 20 to 200 rpm and more preferably 60 to 90 rpm. rpm refers to revolutions per minute, and 1 rpm=1 min−1.
(5) Cell Structure
The cell structure manufactured through the method according to the embodiment of the present invention contains biocompatible macromolecular blocks and cells. In the present invention, a plurality of biocompatible macromolecular blocks are three-dimensionally disposed in gaps between a plurality of cells in a mosaic shape using the biocompatible macromolecular blocks and the cells. Accordingly, it is possible to deliver nutrients to the inside of the cell structure from the outside. In the present specification, in some cases, the cell structure may be referred to as a mosaic cell aggregation (a cell aggregation having a mosaic shape).
In at least a part of the cell structure, the plurality of biocompatible macromolecular blocks are disposed in gaps between the plurality of cells. Here, the “gaps between cells” is not necessarily a space closed by the constituent cells, and may be interposed by the cells. Gaps are not necessarily present between all of the cells, and there may be a place where cells are brought into contact with each other. The distance of gaps between cells through biocompatible macromolecular blocks, that is, the gap distance in a case of selecting a certain cell, and a cell existing in the shortest distance from the certain cell is not particularly limited. However, the distance is preferably the size of a biocompatible macromolecular block, and a favorable distance is also within the range of the favorable size of a biocompatible macromolecular block.
In addition, the biocompatible macromolecular blocks have a configuration of being interposed by the cells. However, there are not necessarily cells between all of the biocompatible macromolecular blocks, and there may be a place where biocompatible macromolecular blocks are brought into contact with each other. The distance between biocompatible macromolecular blocks through cells, that is, the distance in a case of selecting a biocompatible macromolecular block, and a biocompatible macromolecular block existing in the shortest distance from the biocompatible macromolecular block is not particularly limited. However, the distance is preferably the size of an aggregation of cells in a case where one or several cells to be used are gathered. For example, the size thereof is 10 μm to 1,000 μm, preferably 10 μm to 500 μm, and more preferably 10 μm to 200 μm.
In the cell structure, the ratio of a biocompatible macromolecular block to a cell is not particularly limited. However, it is preferable that the ratio of a biocompatible macromolecular block per cell is preferably 0.0000001 μg to 1 μg, more preferably 0.000001 μg to 0.1 μg, more preferably 0.00001 μg to 0.01 μg, and most preferably 0.00002 μg to 0.006 μg. By setting the ratio of the biocompatible macromolecular blocks to the cells to be within the above-described range, it is possible to make the cells more evenly exist. By setting the lower limit to be within the above-described range, it is possible to exhibit an effect of the cells in a case of using the cells for a desired purpose. Moreover, by setting the upper limit to be within the above-described range, it is possible to supply components in arbitrarily existing biocompatible macromolecular blocks to cells. Here, the components in biocompatible macromolecular blocks are not particularly limited, but examples thereof include components contained in a liquid medium.
The thickness or the diameter of the manufactured cell structure is preferably 10 μm to 1 cm or less, more preferably 10 μm to 2,000 μm, even more preferably 15 μm to 1,500 μm, and most preferably 20 μm to 1,300 μm. In a case where the thickness or the diameter of the cell structure is caused to be in the above range, nutrient delivery from the outside to the inside of the cell structure becomes more satisfactory.
In the cell structure according to the embodiment of the present invention, regions consisting of biocompatible macromolecular blocks and regions consisting of cells are preferably disposed in a mosaic shape. In the present specification, the expression “the thickness or the diameter of the cell structure” means the followings. In a case where one point A in the cell structure is selected, in a straight line passing through the point A, a length of the line segment dividing the cell structure such that the distance from an outer boundary of the cell structure is the shortest is set as a line segment A. In the cell structure, the point A at which the line segment A becomes the longest is selected, a length of the line segment A in this case refers to “a thickness or a diameter of a cell structure”.
(6) Use of Sheet-Like Cell Structure
The sheet-like cell structure manufactured by the manufacturing method according to the embodiment of the present invention can be used for cell transplantation. Specifically, the sheet-like cell structure of the present invention can be used for the purpose of transplanting cells into sites with heart diseases such as severe heart failure and severe myocardial infarction and diseases such as cerebral ischemia and cerebral infarction. In addition, the cell structure according to the embodiment of the present invention can also be used for diabetic diseases such as blood circulation disorders in the kidney, the pancreas, the liver, peripheral nerves, the eyes, and the limbs.
As the transplantation method, it is possible to use incision and a method using an endoscope.
The present invention will be more specifically described using the following examples, but is not limited by the examples.
The following CBE3 (which is disclosed in WO2008/103041A) was prepared as recombinant peptides (recombinant gelatin).
CBE3:
Molecular weight: 51.6 kD
Structure: GAP[(GXY)63]3G (SEQ ID NO: 11)
Number of amino acids: 571
RGD sequence: 12
Imino acid content: 33%
Almost 100% of amino acids have a repeating structure of GXY. In the amino acid sequence of CBE3, serine, threonine, asparagine, tyrosine, and cysteine are not included. CBE3 has an ERGD sequence (SEQ ID NO: 10).
Isoelectric point: 9.34
GRAVY value: −0.682
1/IOB value: 0.323
Amino acid sequence (SEQ ID No: 1 in a sequence table) (which is the same as that of SEQ ID No: 3 in WO2008/103041A. However, X in the end is corrected to “P”).
[PTFE Thickness Cylindrical Container]
A cylindrical cup-shaped polytetrafluoroethylene (PTFE) container with a bottom surface thickness of 3 mm, a diameter of 51 mm, a side surface thickness of 8 mm, and a height of 25 mm was prepared. In a case where the curved surface of the cylindrical cup is set as a side surface, the side surface is closed by PTFE with 8 mm and the bottom surface (circular shape of a flat plate) is also closed by PTFE with 3 mm. In contrast, the upper surface is in an open shape. Accordingly, the inner diameter of the cylindrical cup is set to 43 mm. Hereinafter, this container is referred to as a PTFE thickness cylindrical container.
[Aluminum Glass Plate Cylindrical Container]
A cylindrical cup-shaped aluminum container with a thickness of 1 mm and a diameter of 47 mm was prepared. In a case where the curved surface of the cylindrical cup is set as a side surface, the side surface is closed by aluminum with 1 mm and the bottom surface (circular shape of a flat plate) is also closed by aluminum with 1 mm. In contrast, the upper surface is in an open shape. In addition, TEFLON (registered trademark) with a thickness of 1 mm is evenly spread only in the inside of the side surface, and as a result, the inner diameter of the cylindrical cup becomes 45 mm. In addition, the bottom surface of this container enters a state where a 2.2 mm glass plate is joined to the bottom surface thereof on the outside of aluminum. Hereinafter, this container is referred to as an aluminum glass plate⋅cylindrical container.
[Freezing Step in which Difference in Temperature is Small, and Drying Step]
An aqueous CBE3 solution was made to flow into the PTFE thickness cylindrical container and the aluminum glass plate cylindrical container, and was cooled down from the bottom surface within a vacuum freeze dryer (TF5-85ATNNN: Takara Co., Ltd.) using a cooling shelf. A combination of the setting of the final concentration of the aqueous CBE3 solutions in the containers at this time, the amount of solution, and the temperature of the shelf was prepared as described below.
Condition A:
PTFE thickness cylindrical container, final concentration of aqueous CBE3 solution of 4 mass %, amount of aqueous solution of 4 mL. As the setting for the temperature of the shelf, the temperature was cooled down until the temperature reaches −10° C., and then, freezing was performed for 1 hour at −10° C., for 2 hours at −20° C., for 3 hours at −40° C., and finally for 1 hour at −50° C. Thereafter, the frozen product was subjected to vacuum drying for 24 hours at −20° C. after the setting of the temperature of the shelf was returned to −20° C. After 24 hours, the temperature of the shelf was increased to 20° C. in a state in which the vacuum drying was continued as it was, and the vacuum drying was further performed for 48 hours at 20° C. until the vacuum degree was sufficiently decreased (1.9×105 Pa). Then, the product was taken out of the vacuum freeze dryer. Accordingly, a porous body was obtained.
Condition B:
Aluminum glass plate cylindrical container, final concentration of aqueous CBE3 solution of 4 mass %, amount of aqueous solution of 4 mL. As the setting for the temperature of the shelf, the temperature was cooled down until the temperature reaches −10° C., and then, freezing was performed for 1 hour at −10° C., for 2 hours at −20° C., for 3 hours at −40° C., and finally for 1 hour at −50° C. Thereafter, the frozen product was subjected to vacuum drying for 24 hours at −20° C. after the setting of the temperature of the shelf was returned to −20° C. After 24 hours, the temperature of the shelf was increased to 20° C. in a state in which the vacuum drying was continued as it was, and the vacuum drying was further performed for 48 hours at 20° C. until the vacuum degree was sufficiently decreased (1.9×105 Pa). Then, the product was taken out of the vacuum freeze dryer. Accordingly, a porous body was obtained.
Condition C:
PTFE thickness cylindrical container, final concentration of aqueous CBE3 solution of 4 mass %, amount of aqueous solution of 10 mL. As the setting for the temperature of the shelf, the temperature was cooled down until the temperature reaches −10° C., and then, freezing was performed for 1 hour at −10° C., for 2 hours at −20° C., for 3 hours at −40° C., and finally for 1 hour at −50° C. Thereafter, the frozen product was subjected to vacuum drying for 24 hours at −20° C. after the setting of the temperature of the shelf was returned to −20° C. After 24 hours, the temperature of the shelf was increased to 20° C. in a state in which the vacuum drying was continued as it was, and the vacuum drying was further performed for 48 hours at 20° C. until the vacuum degree was sufficiently decreased (1.9×105 Pa). Then, the product was taken out of the vacuum freeze dryer. Accordingly, a porous body was obtained.
[Measurement of Temperature in Each Freezing Step]
Regarding the conditions A to C, the liquid temperature of the surface of water in a center portion of a circle within a container was measured as the liquid temperature (non-cooled surface liquid temperature) of the farthest portion from a cooling side in a solution, and the liquid temperature of a bottom portion within the container was measured as the liquid temperature (cooled surface liquid temperature) of the closest portion to the cooling side in the solution.
As a result, each temperature and a profile of the difference in temperature are as shown in
It can be seen from
Hereinafter, regarding the conditions A to C, the difference in temperature at this time when the non-cooled surface liquid temperature became a melting point (0° C.), the difference in temperature immediately before the temperature of the shelf is decreased from −10° C. to −20° C., and the difference in temperature immediately before the generation of solidification heat will be described. The “difference in temperature immediately before” referred in the present invention indicates the highest temperature in the difference in temperature which can be detected between 1 second to 20 seconds before an event (such as the generation of solidification heat).
Condition A:
Difference in temperature at this time when non-cooled surface liquid temperature became melting point (0° C.): 1.1° C.
Difference in temperature immediately before temperature is decreased from −10° C. to −20° C.: 0.2° C.
Difference in temperature immediately before generation of solidification heat: 1.1° C.
Condition B:
Difference in temperature at this time when non-cooled surface liquid temperature became melting point (0° C.): 1.0° C.
Difference in temperature immediately before temperature is decreased from −10° C. to −20° C.: 0.1° C.
Difference in temperature immediately before generation of solidification heat: 0.9° C.
Condition C:
Difference in temperature at this time when non-cooled surface liquid temperature became melting point (0° C.): 1.8° C.
Difference in temperature immediately before temperature is decreased from −10° C. to −20° C.: 1.1° C.
Difference in temperature immediately before generation of solidification heat: 2.1° C.
The CBE3 porous bodies of Conditions A and B which had been obtained in Reference Example 2 were pulverized using NEW POWERMILL (Osaka Chemical Co., Ltd., NEW POWERMILL PM-2005). The pulverizing was performed for one minute×5 times, that is, for 5 minutes in total at the maximum rotation speed. The sizes of the obtained pulverized substances were divided using a stainless steel sieve to obtain uncross-linked blocks with 25 to 53 μm, 53 to 106 μm, and 106 to 180 μm. Thereafter, biocompatible macromolecular blocks (CBE3 blocks) were obtained by performing thermal cross-linking (six kinds of cross-linking times of 8 hours, 16 hours, 24 hours, 48 hours, 72 hours, and 96 hours) at 160° C. under reduced pressure.
Hereinafter, a porous body derived block under the condition A which has been cross-linked for 48 hours is called E, and a porous body derived block under the condition B which has been cross-linked for 48 hours is called F. E and F are blocks with a small difference in temperature which have been manufactured from porous bodies manufactured through a freezing step in which the difference in temperature is small. There was no influence of the difference in cross-linking time on the performance in the evaluation of the present specification. Therefore, the blocks cross-linked for 48 hours were representatively used. There was no difference in performance between E and F. Hereinafter, the biocompatible macromolecular blocks obtained in Reference Example 3 are also referred to as “petal blocks”. In reference examples, examples, and comparative examples, biocompatible macromolecular blocks which have sizes of 53 to 106 μm, are manufactured under the condition A, and of which the cross-linking time is 48 hours were used.
The tap density is a value indicating how much volume of block can be densely filled. It can be said that, as the value becomes smaller, the block cannot be densely filled, that is, the structure of the block is complicated. The tap density was measured as follows. First, a funnel with an attached cap (having a cylindrical shape with a diameter of 6 mm and a length of 21.8 mm: capacity of 0.616 cm3) at the tip thereof was prepared, and the mass of only the cap was measured. Thereafter, the cap was attached to the funnel, and blocks were poured from the funnel so as to be collected in the cap. After placing a sufficient amount of block, the cap portion was hit 200 times on a hard object such as a desk, the funnel was removed, and the blocks were leveled with a spatula. The mass was measured in a state where the cap was filled up with the blocks. The tap density was obtained by calculating the mass of only the blocks from the difference between the mass of the cap filled up with the blocks and the mass of only the cap, and dividing the mass of only the blocks by the volume of the cap.
As a result, the tap density of the biocompatible macromolecular blocks of Reference Example 3 was 98 mg/cm3.
The cross-linking degree (the number of cross-linking times per molecule) of the blocks cross-linked in Reference Example 3 was calculated. The measurement was performed through a TNBS (2,4,6-trinitrobenzene sulfonic acid) method.
<Preparation of Sample>
A sample (about 10 mg), 4% NaHCO3 aqueous solution (1 mL), and 1 mass % TNBS aqueous solution (2 mL) were added to a glass vial, and the mixture was shaken for 3 hours at 37° C. Thereafter, 37 mass % hydrochloric acid (10 mL) and pure water (5 mL) were added thereto, and then, the mixture was allowed to stand for 16 hours or longer at 37° C. to prepare a sample.
<Adjustment of Blank>
A sample (about 10 mg), 4 mass % NaHCO3 aqueous solution (1 mL), and 1 mass % TNBS aqueous solution (2 mL) were added to a glass vial, 37 mass % hydrochloric acid (3 mL) was immediately added thereto, and the mixture was shaken for 3 hours at 37° C. Thereafter, 37 mass % hydrochloric acid (7 mL) and pure water (5 mL) were added thereto, and then, the mixture was allowed to stand for 16 hours or longer at 37° C. to prepare a blank.
The absorbance (345 nm) of the sample and the blank which had been diluted 10 times with pure water was measured, and the cross-linking degree (the number of cross-linking times per molecule) was calculated from (Formula 2) and (Formula 3).
(As−Ab)/14,600×V/w (Formula 2)
(Formula 2) represents the amount (molar equivalent) of lysine per 1 g of a recombinant peptide.
(in the formula, As represents the sample absorbance, Ab represents the blank absorbance, V represents the amount (g) reaction liquid, and w represents the mass (mg) of a recombinant peptide.)
1−(sample (Formula 2)/an uncross-linked recombinant peptide (Formula 2))×34 (Formula 3)
(Formula 3) represents the number of cross-linking times per molecule.
As a result, the cross-linking degree of the biocompatible macromolecular blocks of Reference Example 3 was 4.2.
The water absorption rate of biocompatible macromolecular blocks manufactured in Reference Example 3 was calculated.
A 3 cm×3 cm nylon mesh bag was filled with about 15 mg of the biocompatible macromolecular blocks at 25° C. and was swollen in ion exchange water for 2 hours. Then, the biocompatible macromolecular blocks were dried with air for 10 minutes, and the mass was measured at each stage to obtain the water absorption rate according to (Formula 4).
Water absorption rate=(w2−w1−w0)/w0 (Formula 4)
(in the formula, w0 represents the mass of a material before water absorption, w1 represents the mass of an empty bag after water absorption, and w2 represents the mass of the entirety of the bag containing the material after water absorption.)
As a result, the water absorption rate of the blocks of Reference Example 3 is 786%.
Human bone marrow-derived mesenchymal stem cells (hMSCs) were suspended in a proliferation medium (Takara Bio Inc.: MSCGM Bullet Kit (trademark)), and biocompatible macromolecular blocks (53 to 106 μm) prepared in Reference Example 3 were added thereto. The mixture was sown in EZSPHERE (registered trademark) DISH 90 mm Type 903 (which had a spheroid well diameter of 800 μm, a spheroid well depth of 300 μm, and about 6,000 spheroid wells, which was a cell non-adhesive dish, in a state in which hMSCs (1.2×108 cells) and biocompatible macromolecular blocks (25 mg) were finally suspended in 23 mL of a medium, in which a bottom surface was a culture surface having a recess portion, and has a side outer wall erected on the periphery of the culture surface, and which was manufactured by AGC TECHNO GLASS CO., Ltd.). At this point, a mixture of biocompatible macromolecular blocks, cells, and a liquid medium was added to the 90 mm dish over the culture surface.
The above 90 mm dish was allowed to stand in a CO2 incubator at 37° C. for five hours (at this point, there was no free biocompatible macromolecular block). Thereafter, the entire contents were transferred to a product name of 30 mL single use bioreactor (BWV-503A manufactured by ABLE Corporation) (second culture container comprising stirring means) by a pipette and allowed to stand for 10 minutes, a supernatant was removed and changed to 30 mL of a new medium, and stirring and culturing were performed at a rotation speed of 70 rpm for 24 hours. As a result, it was possible to successfully manufacture about 6,000 uniform cell structures without fusion and disintegration of the cell structures simultaneously. Manufacturing steps and results are illustrated in
Human bone marrow-derived mesenchymal stem cells (hMSCs) were suspended in a proliferation medium (Takara Bio Inc.: MSCGM Bullet Kit (trademark)), and biocompatible macromolecular blocks (53 to 106 μm) prepared in Reference Example 3 were added thereto. The mixture was sown in EZSPHERE (registered trademark) DISH 90 mm Type 903 (which had a spheroid well diameter of 800 μm, a spheroid well depth of 300 μm, and about 6,000 spheroid wells, which was a cell non-adhesive dish, in a state in which hMSCs (1.2×108 cells) and biocompatible macromolecular blocks (25 mg) were finally suspended in 23 mL of a medium, in which a bottom surface was a culture surface having a recess portion, and has a side outer wall erected on the periphery of the culture surface, and which was manufactured by AGC TECHNO GLASS CO., Ltd.). At this point, a mixture of biocompatible macromolecular blocks, cells, and a liquid medium was added to the 90 mm dish over the culture surface.
The above 90 mm dish was allowed to stand in a CO2 incubator at 37° C. for 23 hours (at this point, there was no free biocompatible macromolecular block). Thereafter, the entire contents were transferred to a product name of 30 mL single use bioreactor (BWV-503A manufactured by ABLE Corporation) (second culture container comprising stirring means) by a pipette and allowed to stand for 10 minutes, a supernatant was removed and changed to 30 mL of a new medium, and stirring and culturing were performed at a rotation speed of 50 rpm for 21 hours. As a result, it was possible to successfully manufacture about 6,000 uniform cell structures without fusion and disintegration of the cell structures simultaneously. Manufacturing steps and results are illustrated in
Human bone marrow-derived mesenchymal stem cells (hMSCs) were suspended in a proliferation medium (Takara Bio Inc.: MSCGM Bullet Kit (trademark)), and biocompatible macromolecular blocks (53 to 106 μm) prepared in Reference Example 3 were added thereto. The mixture was sown in EZSPHERE (registered trademark) DISH 90 mm Type 903 (which had a spheroid well diameter of 800 μm, a spheroid well depth of 300 μm, and about 6,000 spheroid wells, and which was a cell non-adhesive dish, in a state in which hMSCs (1.2×108 cells) and biocompatible macromolecular blocks (25 mg) were finally suspended in 23 mL of a medium, in which a bottom surface was a culture surface having a recess portion, and has a side outer wall erected on the periphery of the culture surface, and which was manufactured by AGC TECHNO GLASS CO., Ltd.). At this point, a mixture of biocompatible macromolecular blocks, cells, and a liquid medium was added to the 90 mm dish over the culture surface.
The above 90 mm dish was allowed to stand in a CO2 incubator at 37° C. for 5 hours and extracted, a large number of individual cells that do not form cell structures were checked, and shapes of the cell structures were not uniform. The results are provided in
Human bone marrow-derived mesenchymal stem cells (hMSCs) were suspended in a proliferation medium (Takara Bio Inc.: MSCGM Bullet Kit (trademark)), and biocompatible macromolecular blocks (53 to 106 μm) prepared in Reference Example 3 were added thereto. The mixture was sown in EZSPHERE (registered trademark) DISH 90 mm Type 903 (which had a spheroid well diameter of 800 μm, a spheroid well depth of 300 μm, and about 6,000 spheroid wells, and which was a cell non-adhesive dish, in a state in which hMSCs (1.2×108 cells) and biocompatible macromolecular blocks (25 mg) were finally suspended in 23 mL of a medium, in which a bottom surface was a culture surface having a recess portion, and has a side outer wall erected on the periphery of the culture surface, and which was manufactured by AGC TECHNO GLASS CO., Ltd.). At this point, a mixture of biocompatible macromolecular blocks, cells, and a liquid medium was added to the 90 mm dish over the culture surface.
The above 90 mm dish was allowed to stand in a CO2 incubator at 37° C. for 49 hours, the fusion of the cell structures was recognized, and it was not able to obtain a large number of cell structures having uniform shapes and sizes. (
[Comparative Example 3] Manufacturing large number of cell structures by stirring and culturing only
Human bone marrow-derived mesenchymal stem cells (hMSCs) were suspended in a growth medium (Takara Bio Inc.: MSCGM BulletKit (Trade Mark)), biocompatible macromolecular blocks (53-106 μm) manufactured in Reference Example 3 was added thereto, hMSC (1.2×108 cells) and biocompatible macromolecular blocks (25 mg) in a state of being suspended in 30 mL of a medium were introduced into a product name of 30 mL single use bioreactor (BWV-503A manufactured by ABLE Corporation) (culture container comprising stirring means), and stirring and culturing were performed at a rotational speed of 55 rpm for 24 hours or 48 hours. As a result, only several tens of nonuniform cell structures (for example, cellular structures having nonuniform shapes and sizes or cell masses only including cells without including biocompatible macromolecular blocks) were present, and it was not possible to obtain a large number of uniform cell structures as in Examples 1 and 2 (
With respect to the cell structures obtained in Examples 1 and 2 and Comparative Examples 1, 2, and 3, the uniformity of the cell structures was evaluated using indexes of fusion avoidance and size uniformity.
With respect to the fusion avoidance, a case where the ratio of the number of manufactured cell structures to the number of multi-wells was 70% or less was B, and a case where the ratio was 70% to 100% was A. That is, with respect to the fusion avoidance, A is more excellent than B. The evaluation results are provided in Table 1.
With respect to the size uniformity, the sizes of the obtained cell structures were evaluated. A case where 70% or more are in the size (the same size means that a case where the size is in ±50% of the median size) is set as A, a case where 40% or more and less than 70% are in the size is set as B, and a case where less than 40% are in the size is set as C. That is, the size uniformity is excellent in A, B is inferior to A, and C is further inferior to B. The evaluation results are provided in Table 1.
In Comparative Example 3, a multi-well was not used, and the fusion avoidance was not able to be measured in terms of an evaluation index, and thus the evaluation was made only based on the size uniformity.
As presented in Table 1, the manufacturing methods of Examples 1 and 2 were excellent in fusion avoidance and size uniformity.
International Application 17F02719 Method of manufacturing cell structure JP18010535 20180316----00150237551800558715 Normal 20180316154500201802231506204110_P1AP101_17_1.app Based on International Patent Cooperation Treaty
| Number | Date | Country | Kind |
|---|---|---|---|
| 2017-052953 | Mar 2017 | JP | national |
This application is a Continuation of PCT International Application No. PCT/JP2018/010535 filed on Mar. 16, 2018, which claims priority under 35 U.S.C § 119(a) to Japanese Patent Application No. 2017-052953 filed on Mar. 17, 2017. Each of the above application(s) is hereby expressly incorporated by reference, in its entirety, into the present application.
| Number | Date | Country | |
|---|---|---|---|
| Parent | PCT/JP2018/010535 | Mar 2018 | US |
| Child | 16573126 | US |
