Patent Application
20240270911
The present invention relates to a method for producing a hydrogel having a porous structure.
In recent years, hydrogels having a polymer network structure have characteristics such as excellent water retention ability and biocompatibility, and thus the hydrogels are materials that are expected to be applied to various use applications such as medical use applications including artificial tissues, scaffold materials for regeneration, sealants, adhesion preventing materials, drug delivery substrates, contact lenses, and the like, and use applications for sensors and surface coating materials (for example, Non Patent Literature 1). In particular, in use applications such as scaffold materials for regeneration, it is desired to develop a polymer material having a μm-scale porous structure.
However, conventionally, in order to obtain the μm-scale porous structure, it has been necessary that a polymer material is produced using a top-down method such as microfabrication of a hydrogel or polymer structure produced in advance by lithography or the like, or a solvent-insoluble polymer raw material. On the other hand, when a solvophilic polymer raw material is used, the material itself is dissolved in the solvent in the first place, or only a hydrogel having a small (nm-scale) porous structure can be produced.
Therefore, an object of the present invention is to provide a hydrogel material having a μm-scale porous structure, and to provide a production method suitable for producing the hydrogel material from a solvophilic polymer raw material.
As a result of diligent studies to solve the above problems, the present inventors have found that a hydrogel having a μm-scale porous structure can be formed by a simple method by performing a gelation reaction in the presence of a high-concentration alkali metal salt, and have completed the present invention. Such a hydrogel has a sponge-like three-dimensional network structure (porous structure) formed by spontaneous phase separation of a polymer as a constituent component in a production process.
That is, in an aspect, the present invention provides as follows:
In another aspect, the present invention also relates to the method for producing a hydrogel, and provides as follows:
According to the production method of the present invention, by adjusting an alkali metal salt concentration in a polymer solution, a hydrogel having a μm-scale porous structure can be easily and efficiently obtained only by mixing the solution.
Since the hydrogel obtained by the production method of the present invention forms a sponge-like, μm-scale three-dimensional network structure (porous structure), the hydrogel may be a material suitable for cell infiltration and adhesion.
Hereinafter, embodiments of the present invention will be described. The scope of the present invention is not limited by these descriptions and can be embodied with modifications as appropriate other than the following exemplary embodiments but not departing from the gist of the present invention.
A production method of the present invention is a method for producing a hydrogel having a porous structure, the production method including the following steps of a) to d):
One of the compounds A and B is a linear (that is, bi-branched), tri-branched, tetra-branched, or octa-branched polyethylene glycol (PEG) having a total of two or more nucleophilic functional groups or electrophilic functional groups in a side chain or at a terminal.
The hydrogel obtained by the production method of the present invention has a sponge-like three-dimensional network structure (porous structure) formed by spontaneous phase separation of a polymer as a constituent component in a production process (hereinafter, such a structure may be referred to as “sponge-like porous structure”). It is also characterized in that the mesh size is on the order of μm much larger than the order of nm obtained in conventional hydrogels. In this hydrogel, a polymer unit is not observed in voids forming a porous structure. That is, the hydrogel as a whole does not have two or more regions where the polymer density is greatly different. Since the polymer unit is not present in the voids, when the hydrogel is compressed by an external force, water can be discharged like a so-called normal sponge. In the production process in the present invention, some or all of the polymer units to be used are not spontaneously solvophilic after a certain period of time. From that time point, the non-solvophilic polymer unit is crosslinked, and as a result, a phase separation structure containing a non-solvophilic polymer as a constituent component is obtained.
In the present specification, the “gel” is generally a dispersion system of a polymer that has high viscosity and lost fluidity, and refers to a state having a relationship of G′≥G″ between a storage modulus G′ and a loss modulus G″. In particular, when a solvent contained in the gel is an aqueous solvent, the gel is referred to as a “hydrogel”.
Hereinafter, the compounds A and B constituting the hydrogel of the present invention and various conditions in various steps will be described.
1-a. Compounds A and B (Gel Constituent Components)
The compounds A and B which are components for forming the hydrogel of the present invention are typically solvophilic polymer species, that is, when the gel is a hydrogel, as the compounds A and B, hydrophilic polymer species can be used. As for the polymer species, polymer species known in the technical field can be used in accordance with the use application, shape, and the like of a final hydrogel as long as they are capable of forming a hydrogel by a gelation reaction (such as a crosslinking reaction) in a solution regardless of the presence or absence of an external stimulus. More specifically, polymer units capable of forming a network structure, particularly a three-dimensional network structure, by crosslinking of the polymer species with each other in the final hydrogel are preferable.
The hydrophilic polymers used as the compounds A and B can be preferably polymers having a polyethylene glycol backbone or a polyvinyl backbone. Typical examples of the polymers having a polyethylene glycol backbone include polymers having a plurality of branches of polyethylene glycol backbones such as two branches, three branches, four branches, or eight branches, and in particular, polymer species having four branches of polyethylene glycol backbones are preferable. Such a gel including a tetra-branched polyethylene glycol backbone is known as a Tetra-PEG gel, and a network-structure network is constructed by an AB-type cross-end coupling reaction between two types of tetra-branched polymers having an electrophilic functional group such as an active ester structure and a nucleophilic functional group such as an amino group at each terminal (Matsunaga et al., Macromolecules, Vol. 42, No. 4, pp. 1344-1351, 2009). Tetra-PEG gels can also be prepared on site easily by simple two-liquid mixing of each polymer solution. By using the Tetra-PEG technique, the gelation time can also be controlled by adjusting the pH and ionic strength during hydrogel preparation. Since the obtained hydrogel contains PEG as a main component, the hydrogel is also excellent in biocompatibility.
Polymers having other than a polyethylene glycol backbone can also be used as long as they can be gelled by crosslinking with each other, and for example, polymers having a polyvinyl backbone such as methyl methacrylate can also be used.
In the production method of the present invention, one of the compounds A and B is a linear, tri-branched, tetra-branched, or octa-branched polyethylene glycol (PEG) having a total of two or more nucleophilic functional groups or electrophilic functional groups in a side chain or at a terminal.
In a preferred embodiment, one of the compounds A and B is PEG and the other can be composed of one or more selected from the group consisting of PEG, a peptide, a protein, a polysaccharide. Examples of the protein include gelatin and albumin. Examples of the polysaccharide include chitosan, hyaluronic acid, and derivatives thereof.
The molecular weight of molecules other than PEG of the compounds A and B is not particularly limited. On the other hand, the molecular weight of PEG is, for example, 2×103 to 100×103 Da, preferably 5×103 to 40×103 Da, and more preferably 10×103 to 20×103 Da. Since PEG tends to be more easily phase-separated as the molecular weight is larger, when the molecular weight is too large, phase separation may occur in a solution state before the crosslinking reaction, which is not preferable. In the present invention, a hydrogel having a porous structure can be obtained by setting the molecular weights of the compounds A and B within a predetermined range and setting the concentration of the alkali metal salt described below within a predetermined range.
In a typical embodiment, both the compounds A and B can be PEG. In this case, the compound A can be a first polymer unit having a total of two or more nucleophilic functional groups in a side chain or at a terminal, the compound B can be a second polymer unit having a total of two or more electrophilic functional groups in a side chain or at a terminal, and a means for reacting these two types of polymer species to crosslink them is suitable. The total of the nucleophilic functional group and the electrophilic functional group is preferably 5 or more. These functional groups are preferably present at a terminal. The content of the first polymer unit can be also larger than the content of the second polymer unit, or the content of the second polymer unit can be larger than the content of the first polymer unit.
Examples of the nucleophilic functional group present in the polymer unit include a thiol group (—SH) (also referred to as a sulfhydryl group), and an amino group, and those skilled in the art can appropriately use a known nucleophilic functional group. Preferably, the nucleophilic functional group is a thiol group or an amino group. The nucleophilic functional groups may be the same as or different from each other, but are preferably the same. When the functional groups are the same, reactivity with an electrophilic functional group that forms a crosslinking bond becomes uniform, and a hydrogel having a homogeneous three-dimensional structure is easily obtained.
As the electrophilic functional group present in the polymer unit, a maleimidyl group or an active ester group can be used. Examples of the active ester group include an N-hydroxy-succinimidyl (NHS) group and a sulfosuccinimidyl group. Those skilled in the art can appropriately use other known electrophilic functional groups. Preferably, the electrophilic functional group is a maleimidyl group. The electrophilic functional groups may be the same as or different from each other, but are preferably the same. When the functional groups are the same, reactivity with a nucleophilic functional group that forms a crosslinking bond becomes uniform, and a hydrogel having a homogeneous three-dimensional structure is easily obtained.
In addition to the combination of the nucleophilic functional group and the electrophilic functional group, a covalent bond forming reaction known to those skilled in the art, such as a cycloaddition reaction with azide and alkyne, or other reaction called click chemistry, can also be appropriately used.
Preferred non-limiting specific examples of the polymer unit having a nucleophilic functional group at a terminal include a compound represented by the following Formula (I) having four branches of a polyethylene glycol backbone and having a thiol group at a terminal.
n11 to n14 may be the same as or different from each other. As the values of nu to n14 are closer to each other, a homogeneous three-dimensional structure can be obtained, and the strength becomes higher. Therefore, in order to obtain a high-strength hydrogel, nu to n14 are preferably the same. When the values of nu to n14 are too high, the strength of the gel is weak, and when the values of n11 to n14 are too low, the gel is hardly formed due to steric hindrance of the compound. Therefore, nu to n14 are, for example, an integer value of 11 to 569, preferably 28 to 228, and more preferably 56 to 114. The molecular weight thereof is, for example, 2×103 to 100×103 Da, preferably 5×103 to 40×103 Da, and more preferably 10×103 to 20×103 Da.
In Formula (I), R11 to R14 are linker moieties connecting a functional group and a core moiety. R11 to R14 may be the same as or different from each other, but are preferably the same in order to produce a high-strength hydrogel having a homogeneous three-dimensional structure. R11 to R14 represent a C1-C7 alkylene group, a C2-C7 alkenylene group, —NH—R15—, —CO—R15—, —R16—O—R17—, —R16—NH—R17—, —R16—CO2—R17—, —R16—CO2—NH—R17—, —R16—CO—R17—, R16—NH—CO—R17—, or —R16—CO—NH—R17—. R15 represents a C1-C7 alkylene group. R16 represents a C1-C3 alkylene group. R17 represents a C1-C8 alkylene group.
The “C1-C7 alkylene group” means an optionally branched alkylene group having 1 or more and 7 or less carbon atoms, and means a linear C1-C7 alkylene group or a C2-C7 alkylene group having one or two or more branches (the number of carbon atoms including the branch is 2 or more and 7 or less). Examples of the C1-C7 alkylene group include a methylene group, an ethylene group, a propylene group, and a butylene group. Examples of the C1-C7 alkylene group include —CH2—, —(CH2)2—, —(CH2)3—, —CH (CH3)—, —(CH2)3—, (CH(CH3))2—, —(CH2)2—CH(CH3)—, —(CH2)3—CH(CH3)—, —(CH2)2—CH(C2H5)—, —(CH2)6—, —(CH2)2—C(C2H5)2—, and —(CH2)3C(CH3)2CH2—.
The “C2-C7 alkenylene group” is a linear or branched alkenylene group having 2 to 7 carbon atoms having one or two or more double bonds in the chain, and examples thereof include divalent groups having double bonds formed by eliminating 2 to 5 hydrogen atoms of adjacent carbon atoms from the alkylene group.
On the other hand, preferred non-limiting specific examples of the polymer unit having an electrophilic functional group at a terminal include a compound represented by the following Formula (II) having four branches of a polyethylene glycol backbone and having a maleimidyl group at a terminal.
In Formula (II), n21 to n24 may be the same as or different from each other. As the values of n21 to n24 are closer to each other, the hydrogel can have a homogeneous three-dimensional structure and has high strength, which is preferable, and n21 to n24 are preferably the same. When the values of n21 to n24 are too high, the strength of the gel is weak, and when the values of n21 to n24 are too low, the gel is hardly formed due to steric hindrance of the compound. Therefore, n21 to n24 are, for example, an integer value of 11 to 569, preferably 28 to 228, and more preferably 56 to 114. The molecular weight of a second tetra-branched compound of the present invention is, for example, 2×103 to 100×103 Da, preferably 5×103 to 40×103 Da, and more preferably 10×103 to 20×103 Da.
In Formula (II), R21 to R24 are linker moieties connecting a functional group and a core moiety. R21 to R24 may be the same as or different from each other, but are preferably the same in order to produce a high-strength gel having a homogeneous three-dimensional structure. In Formula (II), R21 to R24 may be the same as or different from each other, and represent a C1-C7 alkylene group, a C2-C7 alkenylene group, —NH—R25—, —CO—R25—, —R26—O—R27—, —R26—NH—R27—, —R26—CO2—R27—, —R26—CO2—NH—R27—, —R26—CO—R27—, —R26—NH—CO—R27—, or —R26—CO—NH—R27—. R25 represents a C1-C7 alkylene group. R26 represents a C1-C3 alkylene group. R27 represents a C1-C5 alkylene group.
In the present specification, the alkylene group and the alkenylene group may have one or more arbitrary substituents. Examples of the substituent include, but are not limited to, an alkoxy group, a halogen atom (may be any of a fluorine atom, a chlorine atom, a bromine atom, and an iodine atom), an amino group, a mono- or disubstituted amino group, a substituted silyl group, an acyl group, and an aryl group. When the alkyl group has two or more substituents, these substituents may be the same or different. The same applies to alkyl moieties of other substituents including alkyl moieties (for example, alkyloxy groups, aralkyl groups, and the like).
In the present specification, when a certain functional group are defined as “optionally substituted”, the type of substituent, substitution position, and the number of substituents are not particularly limited, and when there are two or more substituents, these substituents may be the same or different. Examples of the substituent include, but are not limited to, an alkyl group, an alkoxy group, a hydroxyl group, a carboxyl group, a halogen atom, a sulfo group, an amino group, an alkoxycarbonyl group, and an oxo group. Substituents may be further present in these substituents.
1-b. Various Conditions in Each Step
The alkali metal salt used in the first and second solutions can be preferably selected from the group consisting of sodium dihydrogen phosphate, disodium hydrogen phosphate, sodium citrate, sodium acetate, potassium sulfate, sodium sulfate, and any combination thereof. At least one of the first and second solutions contains the alkali metal salt.
When the alkali metal salt concentration of the first solution and the second solution are too high, unintended phase separation occurs, which is not preferable. The concentration of the alkali metal salt in the first solution is in a concentration range of 0 to 1000 mM, preferably 0 to 500 mM, and more preferably 0 to 450 mM. Similarly, the concentration of the alkali metal salt in the second solution is in a concentration range of 0 to 1000 mM, preferably 0 to 500 mM, and more preferably 0 to 450 mM. Typically, the lower limit value of the alkali metal salt concentration in either one or both of the first solution and the second solution can be 0.01 mM.
The concentration of the alkali metal salt in the gelling solution (mixed solution before gelation) obtained by mixing the first solution and the second solution is in a concentration range of 300 to 1000 mM, preferably 350 to 500 mM, and more preferably 400 to 450 mM. When the concentration of the alkali metal salt is lower than the range, the crosslinked polymer unit cannot be phase-separated, and a porous structure is not formed. On the other hand, when the concentration of the alkali metal salt is too high, phase separation occurs in a solution state before the polymer unit is crosslinked, which is not preferable.
At the time of mixing in the step c), when the temperature of each solution is too high, unintended phase separation occurs before the start of the crosslinking reaction, and when the temperature thereof is too low, the fluidity of each solution may deteriorate and it may be difficult to handle each solution. Therefore, it is desirable to control the temperature to preferably 10 to 40° C., more preferably 25 to 35° C., and still more preferably 25° C. For example, the first and second solutions can be mixed in a thermostat bath set at the same temperature as each liquid temperature. After the start of the crosslinking reaction between the compounds A and B, the solution temperature may change to some extent. For example, the first and second solutions can also be directly injected into an in vivo environment such as in vivo to form a porous hydrogel in situ.
The term “regardless of the presence or absence of an external stimulus” in the step d) means that gelation proceeds only by mixing the first solution and the second solution without applying an external light stimulus or heat stimulus. Preferably, the external stimulus is a light stimulus.
In the steps c) and d), a time from preparation of the gelling solution to solidification of the gelling solution is preferably 1 second or longer. This makes it possible to ensure a time for mixing the first solution and the second solution. When the time is faster than this, mixing is not successful, and the hydrogel tends to be formed ununiformly, which is not preferable. From another viewpoint, the time until the gelling solution becomes a solid is preferably 5 seconds or longer. In this case, the gelling solution can be poured into a mold as a liquid or directly injected into an in vivo environment after the gelling solution is filled in a syringe barrel, and a porous hydrogel can be molded in a desired shape at a desired location.
1-b. Physical Properties etc. of Hydrogel
The hydrogel obtained by the production method of the present invention is characterized by having a porous structure on the order of μm as described above. The pore size varies depending on conditions such as the total alkali metal salt concentration, and can be, for example, a size of 1 to 500 μm, and is preferably 1 to 100 μm from the viewpoint of mechanical properties of the hydrogel. The pore and the size thereof can be observed by various methods, and as an example, the pore and the size thereof can be measured by bonding a fluorescent dye to a polymer constituting the hydrogel and then acquiring a confocal microscope image. In the hydrogel of the present invention, a polymer unit is not substantially observed in voids forming a porous structure. That is, the hydrogel as a whole does not have two or more regions where the polymer density is greatly different. Since the polymer unit is substantially absent in the voids, when the hydrogel is compressed by an external force, water can be discharged like a so-called normal sponge.
The polymer content in the hydrogel of the present invention is not particularly limited, but in a preferred embodiment, polyethylene glycol is contained in a range of 20 g/L to 250 g/L.
The hydrogel of the present invention has a transmittance lower than the transmittance of the polymer unit before gelation. This is because in the hydrogel of the present invention, the polymer as a constituent component spontaneously phase-separates in a production process. As a result, the poorly soluble polymer behaves as if in a state of phase separation in the solvent, and is not completely transparent but becomes cloudy. Preferably, in the hydrogel of the present invention, a maximum value of transmittance in a wavelength range of 405 nm is transmittance of 80% or less. In terms of such transmittance, the hydrogel of the present invention exhibits completely different properties from a normal hydrogel which is almost transparent.
Preferably, when in a mixed solution of the first solution and the second solution, an equilibrium swelling degree of a hydrogel formed under a condition of a concentration of the alkali metal salt of 200 mM is designated as Qlow, and an equilibrium swelling degree of a hydrogel formed in the presence of an arbitrary concentration of the alkali metal salt is designated as Q, Q satisfies the following relational expression:
The hydrogel of the present invention is also characterized in terms of tensile stress at break. Specifically, when in a mixed solution of the first solution and the second solution, a tensile stress at break of a hydrogel formed under a condition of a concentration of the alkali metal salt of 200 mM is designated as σlow, and a tensile stress at break of a hydrogel formed in the presence of an arbitrary concentration of the alkali metal salt is designated as σ, σ satisfies the following relational expression:
The hydrogel of the present invention can be processed into various shapes such as a thin film according to use applications. Any methods known in this technical field can be used for such processing. For example, in the case of a thin film, the thin film can be obtained, for example, by a method of applying the gelling solution onto a flat substrate such as glass in a state of having fluidity prior to complete solidification.
Hereinafter, the present invention will be described in more detail with reference to Examples; however, the present invention is not limited thereto. In the following Examples, the unit of g/L of the polymer concentration is used, and 1 g/L corresponds to 0.1 wt %.
As a buffer solution of the polymer solution in each experiment, a phosphate buffer solution (PB) was used. The PB contains sodium dihydrogen phosphate and disodium hydrogen phosphate as alkali metal salts. The PB can be prepared by a generally reported method, but here, the PB was prepared to have a pH of 7.4 according to a report by Kurakazu et al. (Macromolecules 2010, 43, 8, 3935-3940). At this time, the buffering capacity of the buffer solution was adjusted by changing the molar concentration (alkali metal salt concentration) of the solute in a range of 0 to 1000 mM.
As raw material polymers, Tetra-PEG-SH (tetrasulfhydryl-polyethylene glycol; NOF CORPORATION, trade name PTE-100SH) having a —SH group at a terminal and Tetra-PEG-OSu (tetrasuccinimidyl-polyethylene glycol; NOF CORPORATION, trade name PTE-100HS) having a succinimidyl group at a terminal were used. The weight average molecular weight (Mw) of both the raw material polymers was 10000.
Tetra-PEG-SH was dissolved in the phosphate buffer solution (PB). At this time, the alkali metal salt concentration of the PB was set to any concentration of 0 to 1000 mM. The PEG concentration was set to any concentration of 20 to 250 g/L.
Tetra-PEG-OSu was dissolved in the PB. At this time, the alkali metal salt concentration of the PB was set to any concentration of 0 to 1000 mM. The PEG concentration was set to any concentration of 20 to 250 g/L.
The first solution (alkali metal salt concentration: 200 mM, PEG concentration: 100 g/L) and the second solution (alkali metal salt concentration: 200 mM, PEG concentration: 100 g/L) were mixed in the same volume ratio in an empty centrifuge tube. This mixed solution was used as a gelling solution containing PEG at a concentration of 100 g/L and an alkali metal salt at a concentration of 200 mM. The gelling solution (1 mL) was put into a 2.5 mL syringe barrel to which a 27G syringe needle (inner diameter: 0.22±0.03) was connected, and discharged into a glass vial. It was visually confirmed that the gelling solution was liquid for at least 5 seconds from the completion of the preparation of the gelling solution to the completion of the discharge. Thereafter, the gelling solution contained in the glass vial was allowed to stand still for 10 minutes without any special external stimulus. When the glass vial was tilted, the gelling solution lost fluidity and became a transparent solid (
The first solution (alkali metal salt concentration: 200 mM, PEG concentration: 250 g/L) and the second solution (alkali metal salt concentration: 200 mM, PEG concentration: 250 g/L) were mixed in the same volume ratio in an empty centrifuge tube. This mixed solution was used as a gelling solution containing PEG at a concentration of 250 g/L and an alkali metal salt at a concentration of 200 mM. The gelling solution (1 mL) was put into a 2.5 mL syringe barrel to which a 27G syringe needle (inner diameter: 0.22±0.03) was connected, and discharged into a glass vial. It was visually confirmed that the gelling solution was liquid for at least 5 seconds from the completion of the preparation of the gelling solution to the completion of the discharge. Thereafter, the gelling solution contained in the glass vial was allowed to stand still for 24 hours without any special external stimulus. When the glass vial was tilted, the gelling solution lost fluidity and became a transparent solid. The obtained transparent hydrogel did not discharge water even when compressed with a finger. It was shown that even if the PEG concentration simply increased as compared to Comparative Example 1, a porous structure was not obtained.
The first solution (alkali metal salt concentration: 400 mM, PEG concentration: 100 g/L) and the second solution (alkali metal salt concentration: 400 mM, PEG concentration: 100 g/L) were mixed in the same volume ratio in an empty centrifuge tube. This mixed solution was used as a gelling solution containing PEG at a concentration of 100 g/L and an alkali metal salt at a concentration of 400 mM. The gelling solution (1 mL) was put into a 2.5 mL syringe barrel to which a 27G syringe needle (inner diameter: 0.22±0.03) was connected, and discharged into a glass vial. It was visually confirmed that the gelling solution was liquid for at least 5 seconds from the completion of the preparation of the gelling solution to the completion of the discharge. Thereafter, the gelling solution contained in the glass vial was allowed to stand still for 10 minutes without any special external stimulus. When the glass vial was tilted, the gelling solution lost fluidity and became a white solid (
The first solution (alkali metal salt concentration: 1000 mM, PEG concentration: 100 g/L) and the second solution (alkali metal salt concentration: 0 mM, PEG concentration: 100 g/L) were mixed in the same volume ratio in an empty centrifuge tube. This mixed solution was used as a gelling solution containing PEG at a concentration of 100 g/L and an alkali metal salt at a concentration of 500 mM. The gelling solution (1 mL) was put into a 2.5 mL syringe barrel to which a 27G syringe needle (inner diameter: 0.22±0.03) was connected, and discharged into a glass vial. It was visually confirmed that the gelling solution was liquid for at least 5 seconds from the completion of the preparation of the gelling solution to the completion of the discharge. Thereafter, the gelling solution contained in the glass vial was allowed to stand still for 24 hours without any special external stimulus. When the glass vial was tilted, the gelling solution lost fluidity and became a white solid. When the obtained hydrogel was compressed with a finger, it was observed that water was discharged.
Similarly, the first solution (alkali metal salt concentration: 0 mM, PEG concentration: 100 g/L) and the second solution (alkali metal salt concentration: 1000 mM, PEG concentration: 100 g/L) were mixed in the same volume ratio in an empty centrifuge tube. This mixed solution was used as a gelling solution containing PEG at a concentration of 100 g/L and an alkali metal salt at a concentration of 500 mM. The gelling solution (1 mL) was put into a 2.5 mL syringe barrel to which a 27G syringe needle (inner diameter: 0.22±0.03) was connected, and discharged into a glass vial. It was visually confirmed that the gelling solution was liquid for at least 5 seconds from the completion of the preparation of the gelling solution to the completion of the discharge. Thereafter, the gelling solution contained in the glass vial was allowed to stand still for 24 hours without any special external stimulus. When the glass vial was tilted, the gelling solution lost fluidity and became a white solid. When the obtained hydrogel was compressed with a finger, it was observed that water was discharged.
These results suggest that it is not essential for the alkali metal salt to be contained in both the first solution and the second solution, and it is sufficient that the alkali metal salt is present in a final gelling solution (mixture).
The first solution (alkali metal salt concentration: 1000 mM, PEG concentration: 100 g/L) and the second solution (alkali metal salt concentration: 1000 mM, PEG concentration: 100 g/L) were mixed in the same volume ratio in an empty centrifuge tube. This mixed solution was used as a gelling solution containing PEG at a concentration of 100 g/L and an alkali metal salt at a concentration of 1000 mM. The gelling solution (1 mL) was put into a 2.5 mL syringe barrel to which a 27G syringe needle (inner diameter: 0.22±0.03) was connected, and discharged into a glass vial. It was visually confirmed that the gelling solution was liquid for at least 5 seconds from the completion of the preparation of the gelling solution to the completion of the discharge. Thereafter, the gelling solution contained in the glass vial was allowed to stand still for 24 hours without any special external stimulus. When the glass vial was tilted, the gelling solution lost fluidity and became a white solid. When the obtained hydrogel was compressed with a finger, it was observed that water was discharged. As described above, it was confirmed that a porous structure was formed even at a relatively high alkali metal salt concentration.
The first solution (alkali metal salt concentration: 600 mM, PEG concentration: 20 g/L) and the second solution (alkali metal salt concentration: 600 mM, PEG concentration: 20 g/L) were mixed in the same volume ratio in an empty centrifuge tube. This mixed solution was used as a gelling solution containing PEG at a concentration of 20 g/L and an alkali metal salt at a concentration of 600 mM. The gelling solution (1 mL) was put into a 2.5 mL syringe barrel to which a 27G syringe needle (inner diameter: 0.22±0.03) was connected, and discharged into a glass vial. It was visually confirmed that the gelling solution was liquid for at least 5 seconds from the completion of the preparation of the gelling solution to the completion of the discharge. Thereafter, the gelling solution contained in the glass vial was allowed to stand still for 24 hours without any special external stimulus. When the glass vial was tilted, the gelling solution lost fluidity and became a white solid. When the obtained hydrogel was compressed with a finger, it was observed that water was discharged. It was confirmed that porositization was possible even at a relatively low PEG concentration (for example, 20 g/L).
In Example 5, sodium dihydrogen phosphate contained in a phosphate buffer solution (PB) and potassium sulfate (K2SO4), which is an alkali metal salt different from disodium hydrogen phosphate, were additionally added to PB in advance. Specifically, K2SO4 was added as a solid to PB prepared so as to have an alkali metal salt concentration of 10 mM so that the K2SO4 concentration was 500 mM, and K2SO4 was dissolved. At this time, the total alkali metal salt concentration was 510 mM in which PB was 10 mM and K2SO4 was 500 mM. The obtained liquid containing K2SO4 was used as the PB, and PEG was dissolved therein at a concentration of 100 g/L to prepare a first solution and a second solution. The first solution (total alkali metal salt concentration: 510 mM, PEG concentration: 100 g/L) and the second solution (total alkali metal salt concentration: 510 mM, PEG concentration: 100 g/L) thus prepared were mixed in the same volume ratio in an empty centrifuge tube. This mixed solution was used as a gelling solution containing PEG at a concentration of 100 g/L and an alkali metal salt at a concentration of 510 mM. The gelling solution (1 mL) was put into a 2.5 ml syringe barrel to which a 27G syringe needle (inner diameter: 0.22±0.03) was connected, and discharged into a glass vial. It was visually confirmed that the gelling solution was liquid for at least 5 seconds from the completion of the preparation of the gelling solution to the completion of the discharge. Thereafter, the gelling solution contained in the glass vial was allowed to stand still for 24 hours without any special external stimulus. When the glass vial was tilted, the gelling solution lost fluidity and became a white solid. When the obtained hydrogel was compressed with a finger, it was observed that water was discharged. This result suggests that the formation of the porous structure does not depend on the type of the alkali metal salt.
In Example 6, sodium dihydrogen phosphate contained in PB and potassium sulfate (K2SO4), which is an alkali metal salt different from disodium hydrogen phosphate, were additionally added to PB in advance. Specifically, K2SO4 was added as a solid to PB prepared so as to have an alkali metal salt concentration of 200 mM so that the K2SO4 concentration was 100 mM, and K2SO4 was dissolved. At this time, the total alkali metal salt concentration was 300 mM in which PB was 200 mM and K2SO4 was 100 mM. The obtained liquid containing K2SO4 was used as the PB, and PEG was dissolved therein at a concentration of 250 g/L to prepare a first solution and a second solution. The first solution (total alkali metal salt concentration: 300 mM, PEG concentration: 250 g/L) and the second solution (total alkali metal salt concentration: 300 mM, PEG concentration: 250 g/L) thus prepared were mixed in the same volume ratio in an empty centrifuge tube. This mixed solution was used as a gelling solution containing PEG at a concentration of 250 g/L and an alkali metal salt at a concentration of 300 mM. The gelling solution (1 mL) was put into a 2.5 mL syringe barrel to which a 27G syringe needle (inner diameter: 0.22±0.03) was connected, and discharged into a glass vial. It was visually confirmed that the gelling solution was liquid for at least 5 seconds from the completion of the preparation of the gelling solution to the completion of the discharge. Thereafter, the gelling solution contained in the glass vial was allowed to stand still for 24 hours without any special external stimulus. When the glass vial was tilted, the gelling solution lost fluidity and became a white solid. When the obtained hydrogel was compressed with a finger, it was observed that water was discharged. This result indicates that a porous structure can be induced at a high PEG concentration (for example, 250 g/L) even when the total alkali metal salt concentration is 300 mM.
As raw material polymers, Linear-PEG-SH (linear sulfhydryl-polyethylene glycol; NOF CORPORATION, trade name DE-100SH) having a —SH group at a terminal and Tetra-PEG-OSu (tetrasuccinimidyl-polyethylene glycol; NOF CORPORATION, trade name PTE-100HS) having a succinimidyl group at a terminal were used. The weight average molecular weight (Mw) of both the raw material polymers was 10000.
Linear-PEG-SH was dissolved in the phosphate buffer solution (PB). At this time, the alkali metal salt concentration of the PB was set to 400 mM. The PEG concentration was set to 200 g/L.
Tetra-PEG-OSu was dissolved in the PB. At this time, the alkali metal salt concentration of the PB was set to 400 mM. The PEG concentration was set to 100 g/L.
The first solution (alkali metal salt concentration: 400 mM, PEG concentration: 200 g/L) and the second solution (alkali metal salt concentration: 400 mM, PEG concentration: 100 g/L) were mixed in the same volume ratio in an empty centrifuge tube. This mixed solution was used as a gelling solution containing PEG at a concentration of 150 g/L and an alkali metal salt at a concentration of 400 mM. The gelling solution (1 mL) was put into a 2.5 mL syringe barrel to which a 27G syringe needle (inner diameter: 0.22±0.03) was connected, and discharged into a glass vial. It was visually confirmed that the gelling solution was liquid for at least 5 seconds from the completion of the preparation of the gelling solution to the completion of the discharge. Thereafter, the gelling solution contained in the glass vial was allowed to stand still for 24 hours without any special external stimulus. When the glass vial was tilted, the gelling solution lost fluidity and became a white solid. When the obtained hydrogel was compressed with a finger, it was observed that water was discharged. This result indicates that the formation of the porous structure does not depend on the number of branches of the polymer constituting the hydrogel.
As one of raw material polymers, Tetra-PEG-OSu (tetrasuccinimidyl-polyethylene glycol-polyethylene glycol; NOF CORPORATION, trade name PTE-100HS) having a succinimidyl group at a terminal was used. The weight average molecular weight (Mw) was 10000. Trilysine (Lys-Lys-Lys, Sigma-Aldrich), which is a kind of peptide, was used as a substance reacting with Tetra-PEG-OSu. The molecular weight of trilysine is 402.53 g/mol.
Trilysine was dissolved in the phosphate buffer solution (PB). At this time, the alkali metal salt concentration of the PB was set to 400 mM. The trilysine concentration was set to 16.10 g/L.
Tetra-PEG-OSu was dissolved in the PB. At this time, the alkali metal salt concentration of the PB was set to 400 mM. The PEG concentration was set to 100 g/L.
The first solution (alkali metal salt concentration: 400 mM, trilysine concentration: 16.10 g/L) and the second solution (alkali metal salt concentration: 400 mM, PEG concentration: 100 g/L) were mixed in the same volume ratio in an empty centrifuge tube to obtain a gelling solution. The gelling solution (1 mL) was put into a 2.5 ml syringe barrel to which a 27G syringe needle (inner diameter: 0.22±0.03) was connected, and discharged into a glass vial. It was visually confirmed that the gelling solution was liquid for at least 5 seconds from the completion of the preparation of the gelling solution to the completion of the discharge. Thereafter, the gelling solution contained in the glass vial was allowed to stand still for 24 hours without any special external stimulus. When the glass vial was tilted, the gelling solution lost fluidity and became a white solid. When the obtained hydrogel was compressed with a finger, it was observed that water was discharged. This result indicates that a porous structure is obtained if either the first solution or the second solution is composed of PEG.
As one of raw material polymers, Tetra-PEG-OSu (tetrasuccinimidyl-polyethylene glycol-polyethylene glycol; NOF CORPORATION, trade name PTE-100HS) having a succinimidyl group at a terminal was used. The weight average molecular weight (Mw) was 10000. Gelatin (Nippi, Incorporated, trade name APAT), which is a kind of protein, was used as a substance reacting with Tetra-PEG-OSu. The molecular weight of gelatin is about 60000 g/mol as a manufacturer's nominal value.
K2SO4 was added as a solid to a phosphate buffer solution (PB) prepared so as to have an alkali metal salt concentration of 200 mM so that the K2SO4 concentration was 500 mM, and K2SO4 was dissolved. At this time, the total alkali metal salt concentration was 700 mM in which PB was 200 mM and K2SO4 was 500 mM. Gelatin was dissolved in the liquid. The gelatin concentration was set to 24 g/L.
K2SO4 was added as a solid to PB prepared so as to have an alkali metal salt concentration of 200 mM so that the K2SO4 concentration was 500 mM, and K2SO4 was dissolved. At this time, the total alkali metal salt concentration was 700 mM in which PB was 200 mM and K2SO4 was 500 mM. Tetra-PEG-OSu was dissolved in the liquid. The PEG concentration was set to 100 g/L.
The first solution (total alkali metal salt concentration: 700 mM, gelatin concentration: 24 g/L) and the second solution (total alkali metal salt concentration: 700 mM, PEG concentration: 100 g/L) were mixed in the same volume ratio in an empty centrifuge tube to obtain a gelling solution. The gelling solution (1 mL) was put into a 2.5 mL syringe barrel to which a 27G syringe needle (inner diameter: 0.22±0.03) was connected, and discharged into a glass vial. It was visually confirmed that the gelling solution was liquid for at least 5 seconds from the completion of the preparation of the gelling solution to the completion of the discharge. Thereafter, the gelling solution contained in the glass vial was allowed to stand still for 24 hours without any special external stimulus. When the glass vial was tilted, the gelling solution lost fluidity and became a white solid. When the obtained hydrogel was compressed with a finger, it was observed that water was discharged. This result indicates that a porous structure can be imparted even when a protein is crosslinked with PEG to obtain a hydrogel.
As one of raw material polymers, Tetra-PEG-OSu (tetrasuccinimidyl-polyethylene glycol-polyethylene glycol; XIAMEN SINOPEG BIOTECH CO., LTD., trade name 4-arm PEG-SC) having a succinimidyl group at a terminal was used. The weight average molecular weight (Mw) was 10000. A polysaccharide was used as a substance reacting with Tetra-PEG-OSu. Examples of the polysaccharide include chitosan and hyaluronic acid, but herein, as an example, chitosan (Santa Cruz Biotechnology, Inc., trade name Carboxymethyl chitosan) was used.
K2SO4 was added as a solid to a phosphate buffer solution (PB) prepared so as to have an alkali metal salt concentration of 200 mM so that the K2SO4 concentration was 0 to 500 mM, and K2SO4 was dissolved. At this time, the total alkali metal salt concentration was 200 to 700 mM in which PB was 200 mM and K2SO4 was 0 to 500 mM. Chitosan was dissolved in the liquid. The chitosan concentration was set to 60 g/L.
K2SO4 was added as a solid to PB prepared so as to have an alkali metal salt concentration of 200 mM so that the K2SO4 concentration was 0 to 500 mM, and K2SO4 was dissolved. At this time, the total alkali metal salt concentration was 200 to 700 mM in which PB was 200 mM and K2SO4 was 0 to 500 mM. Tetra-PEG-OSu was dissolved in the liquid. The PEG concentration was set to 120 g/L.
The first solution (total alkali metal salt concentration: 200 mM, chitosan concentration: 60 g/L) and the second solution (total alkali metal salt concentration: 200 mM, PEG concentration: 120 g/L) were mixed in the same volume ratio in an empty centrifuge tube to obtain a gelling solution. The gelling solution (1 mL) was put into a 2.5 mL syringe barrel to which a 27G syringe needle (inner diameter: 0.22±0.03) was connected, and discharged into a Teflon container. It was visually confirmed that the gelling solution was liquid for at least 5 seconds from the completion of the preparation of the gelling solution to the completion of the discharge. Thereafter, the gelling solution contained in the Teflon container was allowed to stand still for 24 hours without any special external stimulus. When the Teflon container was tilted, the gelling solution lost fluidity and became a transparent solid. The obtained transparent hydrogel did not discharge water even when compressed with a finger.
The first solution (total alkali metal salt concentration: 600 mM, chitosan concentration: 60 g/L) and the second solution (total alkali metal salt concentration: 600 mM, PEG concentration: 120 g/L) were mixed in the same volume ratio in an empty centrifuge tube to obtain a gelling solution. The gelling solution (1 mL) was put into a 2.5 ml syringe barrel to which a 27G syringe needle (inner diameter: 0.22±0.03) was connected, and discharged into a Teflon container. It was visually confirmed that the gelling solution was liquid for at least 5 seconds from the completion of the preparation of the gelling solution to the completion of the discharge. Thereafter, the gelling solution contained in the Teflon container was allowed to stand still for 24 hours without any special external stimulus. When the Teflon container was tilted, the gelling solution lost fluidity and became a white solid. When the obtained hydrogel was compressed with a finger, it was observed that water was discharged. This result indicates that a porous structure can be imparted even when a polysaccharide is crosslinked with PEG to obtain a hydrogel.
As raw material polymers, Tetra-PEG-SH (tetrasulfhydryl-polyethylene glycol; NOF CORPORATION, trade name PTE-100SH) having a —SH group at a terminal and Tetra-PEG-OSu (tetrasuccinimidyl-polyethylene glycol; NOF CORPORATION, trade name PTE-100HS) having a succinimidyl group at a terminal were used. The weight average molecular weight (Mw) of both the raw material polymers was 10000.
K2SO4 was added as a solid to a phosphate buffer solution (PB) prepared so as to have an alkali metal salt concentration of 200 mM so that the K2SO4 concentration was any concentration of 0 to 300 mM, and K2SO4 was dissolved. At this time, the total alkali metal salt concentration was 200 to 500 mM in which PB was 200 mM and K2SO4 was 0 to 300 mM. Tetra-PEG-SH was dissolved in the liquid. The PEG concentration was set to any concentration of 20 to 100 g/L.
K2SO4 was added as a solid to PB prepared so as to have an alkali metal salt concentration of 200 mM so that the K2SO4 concentration was any concentration of 0 to 300 mM, and K2SO4 was dissolved. At this time, the total alkali metal salt concentration was 200 to 500 mM in which PB was 200 mM and K2SO4 was 0 to 300 mM. Tetra-PEG-OSu was dissolved in the liquid. The PEG concentration was set to any concentration of 20 to 100 g/L.
A pair of the first solution (total alkali metal salt concentration: 200 to 500 mM, PEG concentration: 20 to 100 g/L) and the second solution (total alkali metal salt concentration: 200 to 500 mM, PEG concentration: 20 to 100 g/L) having the same total alkali metal salt concentration and PEG concentration were mixed at the same volume ratio in an empty tube to obtain a gelling solution. 200 μL of each of the gelling solutions was poured into a 96-well microplate and left to stand still at 25° ° C. for 24 hours. Thereafter, a photograph of the hydrogel formed in each well was taken (
As raw material polymers, Tetra-PEG-SH (tetrasulfhydryl-polyethylene glycol; NOF CORPORATION, trade name PTE-100SH) having a —SH group at a terminal and Tetra-PEG-OSu (tetrasuccinimidyl-polyethylene glycol; NOF CORPORATION, trade name PTE-100HS) having a succinimidyl group at a terminal were used. The weight average molecular weight (Mw) of both the raw material polymers was 10000.
K2SO4 was added as a solid to a phosphate buffer solution (PB) prepared so as to have an alkali metal salt concentration of 200 mM so that the K2SO4 concentration was any concentration of 0 to 300 mM, and K2SO4 was dissolved. At this time, the total alkali metal salt concentration was 200 to 500 mM in which PB was 200 mM and K2SO4 was 0 to 300 mM. Tetra-PEG-SH was dissolved in the liquid. The PEG concentration was set to 100 g/L. Alexa Fluor™ 594 C5 Maleimide dissolved in dimethyl sulfoxide so as to be 1 mg/mL was additionally added to the prepared Tetra-PEG-SH solution at 1 vol % of the Tetra-PEG-SH solution.
K2SO4 was added as a solid to PB prepared so as to have an alkali metal salt concentration of 200 mM so that the K2SO4 concentration was any concentration of 0 to 300 mM, and K2SO4 was dissolved. At this time, the total alkali metal salt concentration was 200 to 500 mM in which PB was 200 mM and K2SO4 was 0 to 300 mM. Tetra-PEG-OSu was dissolved in the liquid. The PEG concentration was set to 100 g/L.
A pair of the first solution (total alkali metal salt concentration: 200 to 500 mM, PEG concentration: 100 g/L) and the second solution (total alkali metal salt concentration: 200 to 500 mM, PEG concentration: 100 g/L) having the same total alkali metal salt concentration and PEG concentration were mixed at the same volume ratio in an empty tube to obtain a gelling solution. Each gelling solution was poured into a cylindrical mold made of polytetrafluoroethylene (diameter: 15 mm, height: 7 mm) and left to stand still at 25° C. for 24 hours. Thereafter, the hydrogel was removed from the mold. This state was defined as “as-prepared state”, and a photograph of each hydrogel was taken (the upper part of
The equilibrium swelling degree Q of the hydrogel was defined as (d_eq/d_0)3 and plotted (
Specifically, when the value at a total alkali metal salt concentration of 200 mM was designated as Q_low, the value was 1.1*Q_low or more at a total alkali metal salt concentration of 400 mM or more. This corresponds well to the result of the previous microscopic structure observation, and thus it is considered that the generated porous structure affected the value. That is, the presence of the microscopic porous structure can be indirectly determined from the equilibrium swelling degree.
As raw material polymers, Tetra-PEG-SH (tetrasulfhydryl-polyethylene glycol; NOF CORPORATION, trade name PTE-100SH) having a —SH group at a terminal and Tetra-PEG-OSu (tetrasuccinimidyl-polyethylene glycol; NOF CORPORATION, trade name PTE-100HS) having a succinimidyl group at a terminal were used. The weight average molecular weight (Mw) of both the raw material polymers was 10000.
K2SO4 was added as a solid to a phosphate buffer solution (PB) prepared so as to have an alkali metal salt concentration of 200 mM so that the K2SO4 concentration was any concentration of 0 to 250 mM, and K2SO4 was dissolved. At this time, the total alkali metal salt concentration was 200 to 450 mM in which PB was 200 mM and K2SO4 was 0 to 250 mM. Tetra-PEG-SH was dissolved in the liquid. The PEG concentration was set to 100 g/L.
K2SO4 was added as a solid to PB prepared so as to have an alkali metal salt concentration of 200 mM so that the K2SO4 concentration was any concentration of 0 to 250 mM, and K2SO4 was dissolved. At this time, the total alkali metal salt concentration was 200 to 450 mM in which PB was 200 mM and K2SO4 was 0 to 250 mM. Tetra-PEG-OSu was dissolved in the liquid. The PEG concentration was set to 100 g/L.
A pair of the first solution (total alkali metal salt concentration: 200 to 450 mM, PEG concentration: 100 g/L) and the second solution (total alkali metal salt concentration: 200 to 450 mM, PEG concentration: 100 g/L) having the same total alkali metal salt concentration and PEG concentration were mixed at the same volume ratio in an empty tube to obtain a gelling solution. Each gelling solution was poured into a dumbbell-shaped silicone mold defined in JIS K 6251 and left to stand still at 25° C. for 24 hours. Thereafter, the hydrogel was removed from the mold. Each hydrogel was subjected to a tensile test with Autograph AG-X plus (SHIMADZU CORPORATION), and the stress σ at break (tensile stress at break) was recorded. The same test was performed five times for each hydrogel, and the average value and the standard deviation thereof were plotted (
| Number | Date | Country | Kind |
|---|---|---|---|
| 2022-013301 | Jan 2022 | JP | national |
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/JP2023/002236 | 1/25/2023 | WO |
