WO2020048435A1 - 一种聚合物粒子的制备方法 - Google Patents
一种聚合物粒子的制备方法 Download PDFInfo
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- C08J3/00—Processes of treating or compounding macromolecular substances
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- B01J13/00—Colloid chemistry, e.g. the production of colloidal materials or their solutions, not otherwise provided for; Making microcapsules or microballoons
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- C12N5/00—Undifferentiated human, animal or plant cells, e.g. cell lines; Tissues; Cultivation or maintenance thereof; Culture media therefor
- C12N5/0062—General methods for three-dimensional culture
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- C08J—WORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
- C08J2325/00—Characterised by the use of homopolymers or copolymers of compounds having one or more unsaturated aliphatic radicals, each having only one carbon-to-carbon double bond, and at least one being terminated by an aromatic carbocyclic ring; Derivatives of such polymers
- C08J2325/02—Homopolymers or copolymers of hydrocarbons
- C08J2325/04—Homopolymers or copolymers of styrene
- C08J2325/06—Polystyrene
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- C08J2367/00—Characterised by the use of polyesters obtained by reactions forming a carboxylic ester link in the main chain; Derivatives of such polymers
- C08J2367/04—Polyesters derived from hydroxy carboxylic acids, e.g. lactones
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- C08J2405/00—Characterised by the use of polysaccharides or of their derivatives not provided for in groups C08J2401/00 or C08J2403/00
- C08J2405/04—Alginic acid; Derivatives thereof
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- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
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- C08J2405/00—Characterised by the use of polysaccharides or of their derivatives not provided for in groups C08J2401/00 or C08J2403/00
- C08J2405/08—Chitin; Chondroitin sulfate; Hyaluronic acid; Derivatives thereof
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- C08J—WORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
- C08J2433/00—Characterised by the use of homopolymers or copolymers of compounds having one or more unsaturated aliphatic radicals, each having only one carbon-to-carbon double bond, and only one being terminated by only one carboxyl radical, or of salts, anhydrides, esters, amides, imides, or nitriles thereof; Derivatives of such polymers
- C08J2433/04—Characterised by the use of homopolymers or copolymers of compounds having one or more unsaturated aliphatic radicals, each having only one carbon-to-carbon double bond, and only one being terminated by only one carboxyl radical, or of salts, anhydrides, esters, amides, imides, or nitriles thereof; Derivatives of such polymers esters
- C08J2433/06—Characterised by the use of homopolymers or copolymers of compounds having one or more unsaturated aliphatic radicals, each having only one carbon-to-carbon double bond, and only one being terminated by only one carboxyl radical, or of salts, anhydrides, esters, amides, imides, or nitriles thereof; Derivatives of such polymers esters of esters containing only carbon, hydrogen, and oxygen, the oxygen atom being present only as part of the carboxyl radical
- C08J2433/10—Homopolymers or copolymers of methacrylic acid esters
- C08J2433/12—Homopolymers or copolymers of methyl methacrylate
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- C12N—MICROORGANISMS OR ENZYMES; COMPOSITIONS THEREOF; PROPAGATING, PRESERVING, OR MAINTAINING MICROORGANISMS; MUTATION OR GENETIC ENGINEERING; CULTURE MEDIA
- C12N2513/00—3D culture
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- C—CHEMISTRY; METALLURGY
- C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
- C12N—MICROORGANISMS OR ENZYMES; COMPOSITIONS THEREOF; PROPAGATING, PRESERVING, OR MAINTAINING MICROORGANISMS; MUTATION OR GENETIC ENGINEERING; CULTURE MEDIA
- C12N2533/00—Supports or coatings for cell culture, characterised by material
- C12N2533/30—Synthetic polymers
- C12N2533/40—Polyhydroxyacids, e.g. polymers of glycolic or lactic acid (PGA, PLA, PLGA); Bioresorbable polymers
Definitions
- the invention relates to the field of material preparation, in particular to a method for preparing polymer particles.
- Drug-loaded microspheres with a diameter of 50 to 500 microns can be widely used in long-acting release or interventional therapy; polymer porous scaffolds with a diameter of 50 to 2000 microns can be used as carriers for cell culture or drug release carriers; Microspheres can be used for cell separation, and microspheres with fluorescent dyes can be used for detection; double-layered capsules with a diameter of 1 to 4 mm are widely used in the production of perfume packages and pop-up cigarettes.
- the first step is to first establish a dispersion system.
- a dispersion system refers to a system in which one or more substances are dispersed in a certain medium.
- the dispersed substance is called dispersion Phase
- the continuous medium is a dispersion medium or a continuous phase.
- the second step is to solidify the dispersed phase into hard particles by solvent evaporation or polymerization.
- the traditional method of establishing a dispersed phase is generally to divide the dispersed phase into small droplets under the action of a shearing force through a stirring or homogenizer.
- a typical preparation method of polylactic acid microspheres polylactic acid is dissolved in chloroform as a dispersed phase; an aqueous solution of PVA and Span 80 (span80) is a continuous phase. The two are mixed to obtain the upper layer.
- the layered system is water and the lower layer is chloroform. Place the system on a stirrer and turn on the machine.
- the trichloromethane solution of polylactic acid will be dispersed into small droplets due to the shearing action of the suspension. In the dispersed phase.
- the traditional solvent volatilization or polymerization reaction to prepare polymer particles generally requires a long time stirring after the dispersion system is established so that the dispersed phase is suspended in the dispersion medium.
- the preparation of typical polylactic acid microspheres is continued as an example. After the system is established, it is necessary to continue stirring for more than ten hours to allow chloroform to evaporate in order to obtain solid particles.
- the following problems may exist:
- the stirring force is not enough, and the droplets are aggregated at the bottom or upper part due to gravity.
- the stirring force is too strong, and the stirring shearing force may cause the droplets to break up again.
- the technical problem to be solved by the present invention is to provide a method for preparing polymer particles, which can obtain particles with good uniformity.
- the present invention provides a method for preparing polymer particles:
- the gel is dissolved.
- the functional material may be uniformly distributed in the polymer solution and / or the reactive monomer in a homogeneous state, or may be in a heterogeneous state. , Is dispersed or encapsulated in a polymer solution and / or a reactive monomer.
- the gelable solution encapsulating the droplets forms gel fibers after gelation in the coagulation bath.
- the gelled solution containing the droplets is added to a coagulation bath while the coagulation bath is moved relative to the discharge port 100.
- the gel fibers are stretched while the gel fibers are being formed.
- the droplets are wrapped by a gelable solution while the droplets are being formed.
- the droplets are wrapped by a gelable solution while the droplets are being formed, and the droplet forming and wrapping device is used to complete the droplet formation.
- the droplet formation wrapping device includes:
- the first cavity communicates with the second cavity through a droplet forming hole.
- a conduit is provided at the outlet of the second pipeline and the fifth pipeline.
- the gelable solution is an ion-sensitive system solution, or a pH-sensitive system solution, or a temperature-sensitive solution.
- the ion-sensitive system solution is a sodium alginate solution—a polyvalent salt solution system.
- the pH-sensitive system solution is a chitosan hydrochloric acid solution-sodium hydroxide solution system.
- the temperature-sensitive solution is a poloxamer solution.
- the functional material is one or more of protein molecules, or drug molecules, or nanoparticles, or magnetic particles, or fluorescent dyes, or flavors, or fragrances, or pore-forming agents, or quantum dots.
- the combination is one or more of protein molecules, or drug molecules, or nanoparticles, or magnetic particles, or fluorescent dyes, or flavors, or fragrances, or pore-forming agents, or quantum dots. The combination.
- the polymer solution is a polylactic acid-glycolic acid copolymer solution, or a polylactic acid solution, or a polymethyl methacrylate solution, or a combination of one or more of the polycaprolactone solutions;
- the reactive monomer is, or styrene, or a combination of one or more of divinylbenzene, acrylic acid, and methacrylic acid.
- the method for preparing polymer particles provided by the present invention has the following advantages:
- the droplets formed by the polymer solution and / or reactive monomer containing functional materials are solidified in the environment after the gelled solution is wrapped and formed into a gel. Due to the huge viscosity of the gel, the droplets do not Collisions will occur, no aggregation effect will occur, no stirring is required during the solvent volatilization and solidification process, and the damage of the droplets by the shear force is avoided, so that particles with good uniformity can be obtained.
- a surfactant is used to reduce the surface tension to maintain the stability of the droplets.
- a surfactant may not be used.
- FIG. 1 is a preparation flow chart of the present invention
- FIG. 1 three forms of droplet formation according to the present invention.
- the functional materials are uniformly distributed in the polymer solution and / or the reactive monomer in a homogeneous state;
- the functional materials are uniformly dispersed in the polymer solution and / or the reactive monomer in a heterogeneous state;
- FIG. 3 is a schematic structural diagram of a droplet forming and wrapping device according to an embodiment of the present invention.
- FIG. 4 is a schematic structural diagram of another droplet forming and wrapping device according to an embodiment of the present invention.
- FIG. 5 is a schematic structural diagram of a droplet forming and wrapping device with a stretching structure according to an embodiment of the present invention
- FIG. 6 is a schematic structural diagram of a third type of droplet forming and wrapping device according to an embodiment of the present invention.
- FIG. 7 is a schematic structural diagram of a fourth droplet forming and wrapping device according to an embodiment of the present invention.
- Example 8 is a photomicrograph of a droplet in a gel in Example 1 of the present invention.
- Example 9 is a photomicrograph of a 100 micron particle in Example 1 of the present invention.
- FIG. 10 is a particle light micrograph of the seventh embodiment.
- 61 first cavity
- 62 second cavity
- 63 droplet formation hole
- an embodiment of the present invention provides a method for preparing polymer particles.
- the method includes the following steps:
- a polymer solution and / or a reactive monomer 71 containing a functional material is formed into droplets 711;
- the gel is dissolved.
- the polymer solution and / or the reactive monomer 71 containing the functional material is a dispersed phase
- the gelable solution 72 is a continuous phase to make the gelable
- the gelation of the solution 72 is a coagulation bath 73.
- mechanical particles are generally used to prepare polymer particles.
- the process is as follows.
- the dispersed phase is added to the dispersion medium, a suitable surfactant is added, and the dispersed phase is turned into a liquid by stirring or a homogenizer.
- the drops are dispersed in a dispersion medium.
- the solvent is volatilized or the monomers are polymerized through long-term stirring to obtain solid polymer particles.
- the dispersed phase still needs a long time to volatilize the solvent or carry out the polymerization reaction.
- Continuous stirring at this stage will cause the formed particles to aggregate due to interfacial tension, gravity, collision, etc.
- the shearing force is broken due to stirring, or the shearing force is different due to the different flow velocity of each point in the container, which causes the particle size distribution to widen.
- the method for preparing the polymer particles provided in the embodiment of the present invention, because the dispersed phase is confined in the gel, the particles cannot be brought into contact, and there is no traditional due to interfacial tension, gravity, or collision. Aggregation, or fragmentation due to agitated shearing forces, or different shearing forces due to different flow rates at various points in the container, and other problems such as widening of particle size distribution. This makes it possible to produce uniform particles.
- the functional materials in the examples of the present invention refer to ingredients added in order to make the prepared particles have certain uses.
- the component can be a drug, a nanoparticle, a porogen, a fluorescent dye, a fragrance, or the like.
- the functional material in the preparation of drug sustained-release microspheres, is a drug molecule; in the preparation of magnetic microspheres, the functional material is ferric oxide nanoparticles; in the preparation of fluorescent microspheres, the functional material is fluorescent dye or quantum Point; when preparing bead microspheres, it is the inner layer of spices or flavor substances.
- the functional material 01 in this embodiment can be uniformly distributed in the polymer solution in a homogeneous state, or uniformly in a reactive monomer in a homogeneous state, or uniformly in a polymerized special solution in a homogeneous state.
- the mixed liquid with the reactive monomer is shown in Fig. 2a.
- the functional material 01 in this embodiment may also be dispersed in a polymer solution in a heterogeneous state, or in a reactive monomer, or in a mixed liquid composed of a polymer solution and a reactive monomer, such as Figure 2b.
- the functional material 01 in this embodiment may also be wrapped in a polymer solution or a reactive monomer in a heterogeneous state, or in a mixed liquid composed of a polymer solution and a reactive monomer, such as Figure 2c.
- step 103 the droplet 711 is wrapped by the gelable solution 72, and generally, the droplet 711 is wrapped by the gelable solution at the same time as the droplet 711 is formed. .
- a droplet 711 forming and wrapping device is used to realize the formation and wrapping of the droplet 711.
- the structure thereof is shown in FIG. 3, and the device includes a polymer solution and / or a reactive monomer for containing functional materials.
- the polymer solution and / or the reactive monomer containing the functional materials are fed into the first pipe 31, and the condensable is fed into the second pipe 32 at the same time.
- Gelatinized solution When this structure is used to achieve the formation and wrapping of the droplets 711, the polymer solution and / or the reactive monomer containing the functional materials are fed into the first pipe 31, and the condensable is fed into the second pipe 32 at the same time. Gelatinized solution.
- the flow velocity of the liquid in the first pipeline 31 and the second pipeline 32 is controlled.
- the velocity of the fluid in the inner and outer pipelines is relatively low, one droplet 711 will be formed directly at the outlet; when the velocity of the fluid in the inner and outer pipelines is higher, a coaxial fluid will be formed first.
- the outer layer gels to form gel fibers, and the liquid inside the gel fibers changes from a continuously flowing liquid into droplets 711 under the effect of interfacial tension.
- the droplets 711 are in a single row. The order is arranged inside the gel fibers. With this structure, since all the droplets 711 are formed through the first pipe 31, the uniformity of the formed droplets 711 is excellent.
- the wrapping device 711 includes a third pipeline 41 for flowing a liquid containing functional materials, and is sleeved outside the third pipeline 41 and is coaxial with the third pipeline 41 for supplying a polymer solution and / or The fourth pipeline 42 through which the reactive monomer flows, and the fifth pipeline 43 sleeved outside the fourth pipeline 42 and coaxial with the fourth pipeline 42 and used for flowing the gelable solution.
- the polymer solution and / or the reactive monomer are fed into the fourth pipe 42 while the liquid containing the functional material is fed into the third pipe 41, At the same time, a gelable solution is sent to the fifth line 43.
- the third pipeline 41 and the fourth pipeline 42 are controlled to use the flow velocity of the liquid in the fifth pipeline 43.
- the velocity of the fluid in the three pipelines is relatively low, droplets 711 are formed directly at the outlet.
- the center of the droplet 711 is a functional material, and the outer layer of the droplet 711 is a polymer solution.
- the droplet 711 is wrapped by a gelable solution; when the fluid velocity of the three pipelines is high, a coaxial fluid is formed first, and then the outermost layer is gelled to form Gel fibers, and the liquid inside the gel fibers changes from a continuously flowing liquid into droplets 711 under the effect of interfacial tension.
- the droplets 711 are arranged in a single row in an orderly manner inside the gel fibers. At this time, the center of the droplet 711 is a functional material, and the outer layer of the droplet 711 is a polymer solution and / or a reactive monomer.
- the liquid droplet 711 forming wrapping device of this embodiment may also adopt a structure as shown in FIG. 6, which includes a first cavity 61 for placing a polymer solution containing a functional material and / or a reactive monomer; A second cavity 62 for the gelable solution to flow; the first cavity 61 and the second cavity 62 communicate with each other through a droplet forming hole 63.
- a polymer solution containing functional materials and / or a reactive monomer are passed into the first cavity 61, and the polymer containing functional materials in the first cavity 61 is passed.
- the solution and / or reactive monomer will flow to the second cavity 62 through the droplet formation hole 63, and form a droplet 711 when entering the second cavity 62, and attach to the inner wall of the second cavity 62, and at the same time, go to the second cavity
- a gelatinizable solution is passed into 62, and the droplets 711 attached to the inner wall of the second cavity 62 are washed out by the gelable solution to complete the encapsulation of the droplets 711 by the gelable solution.
- Both the first cavity 61 and the second cavity 62 in this structure are preferably tubular cavities. Of course, it is also possible to divide a cavity into two parts through a partition, one of which is the first cavity 61 and the other is the second cavity 62, and the droplet forming hole 63 is provided on the partition. At this time, the The shape is not limited.
- the first cavity 61 is a pipeline
- the second cavity 62 is also a pipeline
- the droplet formation hole 63 is the first cavity 61.
- the principle and process of forming and wrapping liquid droplets 711 are the same as those of the device for forming and wrapping liquid droplets 711 shown in FIG. 6.
- step 105 a gelable solution coated with droplets 711 is added to a coagulation bath 73, so that the gelable solution coated with droplets 711 is gelled.
- the solution was gelled to form a gel 722.
- the gelatinizable solution containing the liquid droplets 711 is added to the coagulation bath 73, which may be performed by a dropwise method or by an injection method.
- the discharge port 100 is located above the coagulation bath 73.
- the discharge port 100 here refers to an outlet of the gelable solution wrapped with the droplets 711. After the gelable solution wrapped with the liquid droplets 711 formed at the discharge port 100 is dropped into the coagulation bath 73, the gelable solution forms a gel.
- the discharge port 100 is submerged in the coagulation bath 73.
- the gelable solution wrapped with the droplets 711 forms gel fibers at the discharge opening 100.
- the gelable solution forms gel fibers with a certain strength immediately after encountering the coagulation bath 73, not only the stability of the droplet 711 can be maintained, but droplets with a smaller particle size can be more easily obtained. 711.
- the gelable solution containing the droplets 711 is added to the coagulation bath 73 by an injection method to form gel fibers.
- the gel fiber will be continuously generated at the discharge port 100, causing the gel fiber to bend or fold, and the droplets 711 inside the gel fiber are deformed or aggregated due to being squeezed, which affects its morphology and uniformity.
- the coagulation bath 73 is moved relative to the discharge port 100 while the gelable solution wrapped with the liquid droplets 711 is added to the coagulation bath 73.
- the gel fibers are sequentially stacked in the coagulation bath 73, so that the internal droplets 711 caused by the excessive bending of the fibers are not deformed or agglomerated due to compression, It is beneficial to obtain particles with good uniformity.
- the coagulation bath 73 moves relative to the discharge port 100.
- the coagulation bath 73 may be rotated by an external device, or the discharge port 100 may be rotated by an external device.
- the formed gel fiber can be stretched by setting the traction device 800.
- stretching the formed fibers not only the orderly arrangement of the fibers can be achieved, but the internal droplets 711 caused by the excessive bending of the fibers can be prevented from deforming or agglomerating due to extrusion, which is beneficial for obtaining uniform particles; It is possible to change the diameter of the droplet 711 by drawing fine fibers, and obtain a droplet 711 having a smaller diameter.
- a duct may be provided at the discharge port 100 of the structure shown in FIG. 3 and FIG. 4.
- the process of gelation of the gelled solution is delayed, and the polymer solution and / or reactive monomer containing functional materials can be formed into droplets 711 in the gelable solution to avoid formation.
- the situation with coaxial fibers occurs.
- the gelable solution in the embodiment of the present invention may be an ion-sensitive system solution, a pH-sensitive system solution, or a temperature-sensitive solution.
- the ion-sensitive system solution preferably uses a sodium alginate solution—a polyvalent salt solution system, which can be a sodium alginate-calcium chloride system.
- a sodium alginate solution will form an ion-crosslinked gel when it meets the calcium chloride solution, and the gel can be re-dissolved by using sodium citrate. Polymer particles can be obtained at a lower cost.
- a chitosan-sodium hydroxide solution system can be preferably used as the pH-sensitive system solution.
- Chitosan is dissolved in a 2% acetic acid aqueous solution.
- alkaline solutions such as sodium hydroxide and potassium hydroxide, it will solidify into gel fibers.
- the gel fibers can be re-dissolved by adding acid again. Polymer particles can be obtained at a lower cost.
- the temperature-sensitive solution may be preferably a poloxamer solution.
- the poloxamer solution is liquid at low temperature, and it can also be transformed into a gel state when injected into an empty container at high temperature.
- Example 1 Preparation of drug-loaded polylactic acid-glycolic acid copolymer (PLGA) embolized microspheres for interventional therapy
- PLGA polylactic acid-glycolic acid copolymer
- This embodiment uses the liquid droplet 711 shown in FIG. 3 to form a wrapping device:
- the inner diameter of the first pipeline 31 is 0.25 mm and the outer diameter is 0.48 mm; the inner diameter of the second pipeline 32 is 0.75 mm and the outer diameter is 1.10 mm.
- the first pipeline 31 and the second pipeline 32 are They were all submerged in the coagulation bath 73, and 100%, 120 microns, 160 microns, 200 microns, 220 microns, 240 microns, and 100 micron in diameter were prepared.
- the functional material in this embodiment is a paclitaxel drug molecule, which is uniformly distributed in the droplets 711 in a homogeneous form.
- Solution preparation Disperse phase solution, a certain amount of PLGA is dissolved in chloroform, and the corresponding solution is configured according to the mass fraction of 0.5%, 1%, 3%, 5%, 8%, and 10%, and then according to the PLGA The ratio of mass to drug mass was 10: 1, and paclitaxel was added separately.
- Configure the outer layer continuous phase solution Weigh 1g of sodium alginate and dissolve it in 100g of deionized water. In order to improve the hydrophilicity of the microsphere surface, 1g of polyvinyl alcohol (PVA) is added.
- PVA polyvinyl alcohol
- Configure a coagulation bath 73 Weigh 1 g of calcium chloride and dissolve it in 1000 g of deionized water.
- the flow rates of all samples were set as follows: the flow rate of the dispersed phase solution through the first line 31 was set at 60 ml / hour, the flow rate of the continuous phase solution through the second line 32 was set at 300 ml / hour, and the speed of the coagulation bath 73 was 20 rpm.
- the dispersed phase solution droplets 711 are surrounded by gel fibers formed by the continuous phase solution and flow out from the nozzle uniformly, and are collected in the coagulation bath 73.
- the obtained gel fiber containing one droplet 711 was dried in water, and the chloroform was completely evaporated.
- FIG. 6 is a light microscope photograph of droplets 711 in the gel
- FIG. 7 is a light microscope photograph of 100 micron particles after separation.
- the drug-loaded microspheres can be directly introduced into the patient through a microcatheter and blocked in the tumor blood vessels.
- the microspheres can block tumor blood vessels and block tumor feeding, on the other hand, the drugs released by the drug-loaded microspheres can inhibit and kill tumor cells and play a dual antitumor effect.
- the drug-loaded microspheres prepared by the method of the present invention have the advantages of uniform size and completely controllable size, and thus can fully meet the strict clinical requirements for the size of drug-loaded microspheres (embolized microspheres).
- the porous spherical cell scaffold needs to have a suitable volume size, and preferably has a through-channel structure.
- the spherical scaffold has good rolling properties, and the cells grow on its surface or in the internal channels, which is suitable for large-scale 3D culture.
- the functional material is a porogen sodium bicarbonate aqueous solution, which is dispersed in the droplets 711 in a heterogeneous form.
- This embodiment uses the droplet 711 shown in FIG. 3 to form a wrapping device: the inner diameter of the first pipe 31 is 0.35 mm and the outer diameter is 0.65 mm; the inner diameter of the second pipe 32 is 1.15 mm and the outer diameter of the pipe is 1.50mm, prepare a spherical cell culture scaffold with a diameter of about 0.8mm.
- Configure a coagulation bath 73 Weigh 1 g of calcium chloride and dissolve it in 1000 g of deionized water.
- the flow rate of the dispersed phase solution through the first line 31 is set at 60 ml / hour, and the flow rate of the continuous phase solution through the second line 32 is set at 300 ml / hour.
- the coagulation bath 73 is rotated at a speed of 20 rpm.
- the dispersed phase solution droplets 711 are wrapped by the gel fibers formed by the continuous phase solution one by one and flow out uniformly from the discharge port 100 and are collected in the coagulation bath 73.
- the obtained gel fiber containing the droplet 711 was dried in water, and the dichloromethane was completely evaporated. Sodium citrate was then added to depolymerize the fibers (the drying and depolymerization processes were the same as in Example 1). A uniform pellet with a diameter of 800 microns was obtained.
- the obtained pellet was stirred in 0.1M sodium hydroxide for 1 hour to obtain a porous spherical cell culture scaffold having a through channel and a uniform microsphere size.
- This embodiment uses the liquid droplet 711 shown in FIG. 3 to form a wrapping device:
- the inner diameter of the first pipeline 31 is 0.24 mm and the outer diameter is 0.45 mm; the inner diameter of the second pipeline 32 is 0.7 mm and the outer diameter is 1.06 mm.
- the functional material is ferric oxide particles, which are dispersed in the droplets 711 in a heterogeneous form.
- a coagulation bath 73 was configured: 1 g of calcium chloride was dissolved in 1000 ml of deionized water.
- the flow rate of the dispersed phase solution through the first line 31 is set at 40 ml / hour, and the flow rate of the continuous phase solution through the second line 32 is set at 400 ml / hour.
- the dispersed phase solution droplets 711 are wrapped by the gel fibers formed by the continuous phase solution one by one and flow out uniformly from the discharge port 100 and are collected in the coagulation bath 73.
- the temperature of the coagulation bath 73 was raised to 90 degrees Celsius, and the microspheres were allowed to react and solidify at this temperature for 1 hour. After the microspheres are completely cured, sodium citrate is used to depolymerize the fibers (the depolymerization process is the same as in Example 1) to obtain magnetic microspheres with a diameter of 380 microns.
- the explosion beads produced on the market are oily explosion beads, and the inside is mineral oil, liquid paraffin substances, which are harmful to the human body.
- the size of the blasting ball is from 2mm to 4mm, and it is difficult to ensure that the traditional water / oil / water system is not broken.
- a droplet 711 is used to form a wrapping device as shown in FIG. 4.
- the inner diameter of the third pipe 41 is 0.75 mm and the outer diameter is 1.10 mm.
- the inner diameter of the fourth pipe 42 is 1.65 mm and the outer diameter is 2.15. mm;
- the fifth pipe 43 has an inner diameter of 3.50 mm and an outer diameter of 4.00 mm.
- the aqueous solution of the functional material menthol is wrapped in the droplets 711 in a heterogeneous form.
- the inner layer uses an aqueous system: we dissolve 0.5 g of menthol as a flavor substance in 1000 ml of deionized water.
- Intermediate layer dispersed phase solution (oil phase): Polymethyl methacrylate (PMMA) was used as a capsule wall material and dissolved in a mixed solvent of ethyl acetate and dichloromethane.
- PMMA Polymethyl methacrylate
- Outer continuous phase solution 1 g of sodium alginate was dissolved in 100 ml of deionized water.
- a coagulation bath 73 was configured: 1.5 g of calcium chloride was dissolved in 1000 ml of deionized water.
- the flow rate of the aqueous phase solution through the third line 41 is set at 60 ml / hour
- the flow rate of the oil phase of the fourth line 42 is 60 ml / hour
- the flow rate of the water phase of the fifth line 43 is 300 ml / hour.
- the coagulation bath 73 was rotated at 10 rpm. After the obtained fiber gel containing the droplet 711 is dried in water (the drying process is the same as in Example 1), a PMMA-encapsulated liquid pop-up capsule with a particle diameter of about 3 mm is prepared.
- Embodiment 5 Preparation of Polylactic Acid Microspheres by Using Chitosan Acetic Acid Solution as the Outer Layer
- This embodiment uses the droplet 711 shown in FIG. 5 to form a wrapping device:
- the inner diameter of the first pipeline 31 is 0.25 mm and the outer diameter is 0.48 mm; the inner diameter of the second pipeline 32 is 0.75 mm and the outer diameter is 1.10 mm.
- Disperse phase solution in inner layer take 5g of polylactic acid and dissolve in 95ml of dichloromethane;
- Outer continuous phase solution 5g of chitosan was dissolved in 100ml of 2% acetic acid aqueous solution;
- Coagulation bath 73 Take 500 grams of sodium hydroxide and dissolve in 5 liters of ethanol solution.
- the flow rate of the dispersed phase solution through the first line 31 is set at 20 ml / hour, and the flow rate of the continuous phase solution through the second line 32 is set at 100 ml / hour.
- the dispersed phase solution droplets 711 are surrounded by gel fibers formed by the continuous phase solution and flow out from the nozzle uniformly, and are collected in the coagulation bath 73.
- the microsphere size can be adjusted by the pulling speed of the traction device 800.
- the obtained gel fibers each containing droplets 711 were dried in water, and then acetic acid was added to dissolve the shell of the chitosan fiber to obtain polylactic acid particles having a diameter of 200 microns.
- the liquid droplet 711 shown in FIG. 6 is used to form a wrapping device, wherein the inner wall of the first cavity 61 is a tubular film and the tubular film is a tetrafluoroethylene film with an inner diameter of 3 mm.
- the film has uniform small holes with average holes. The diameter is 0.7mm.
- Disperse phase solution in inner layer take 5g of polycaprolactone and dissolve in 95ml of dichloromethane;
- Outer continuous phase solution take 0.75g of sodium alginate and dissolve in 100ml of deionized water;
- Coagulation bath 73 Weigh 1 g of calcium chloride and dissolve it in 1000 ml of deionization.
- the dispersed phase solution flow rate was set at 200 ml / hour, and the outer continuous phase solution flow rate was set at 2000 ml / hour.
- the dispersed phase solution droplets 711 are surrounded by gel fibers formed by the continuous phase solution and flow out uniformly from the nozzle, and are collected in the coagulation bath 73.
- the obtained gel fiber containing the droplet 711 was dried in water, and then sodium citrate was added to depolymerize the fiber (the drying and depolymerization processes are the same as those in Example 1).
- Polycaprolactone (PCL) particles having a diameter of about 0.36 mm can be obtained.
- the liquid droplet 711 shown in FIG. 7 is used to form a wrapping device, wherein the second cavity 62 is a pipe with an inner diameter of 1 mm, and the first cavity 61 is a pipe with an inner diameter of the pipe of 0.2 mm.
- Disperse phase solution in inner layer take 3g of polycaprolactone and dissolve in 97ml of dichloromethane;
- Outer continuous phase solution take 1g of sodium alginate and dissolve in 100ml of deionized water;
- Coagulation bath 73 Weigh 1 g of calcium chloride and dissolve it in 1000 ml of deionization.
- the flow rate of the dispersed phase solution through the first cavity 61 is set at 15 ml / hour, and the flow rate of the continuous phase solution through the second cavity 62 is set at 150 ml / hour.
- the dispersed phase solution droplets 711 are surrounded by gel fibers formed by the continuous phase solution and flow out from the vertical main pipe outlet one by one, and are collected in the coagulation bath 73.
- the obtained gel fibers each containing droplets 711 were dried in water, and then sodium citrate was added to depolymerize the fibers (the drying and depolymerization processes are the same as in Example 1).
- PLGA particles with a diameter of about 0.16 mm can be obtained.
- Figure 8 is a particle light micrograph.
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Abstract
Description
Claims (16)
- 一种聚合物粒子的制备方法,其特征在于,将含有功能性物料的聚合物溶液和/或反应性单体,形成液滴;通过可凝胶化的溶液包裹所述液滴;将包裹有所述液滴的可凝胶化的溶液加入到凝固浴中,以使得包裹有所述液滴的可凝胶化的溶液凝胶化,形成凝胶;在凝胶内部形成粒子后,溶解所述凝胶。
- 根据权利要求1所述的制备方法,功能性物料以均相的状态均匀分布在聚合物溶液和/或反应性单体中,或者以非均相的状态,被分散或者被包裹在聚合物溶液和/或反应性单体中。
- 根据权利要求1或2所述的制备方法,其特征在于,包裹有所述液滴的可凝胶化的溶液在所述凝固浴中凝胶化后形成凝胶纤维。
- 根据权利要求1至3任意一项所述的制备方法,其特征在于,将包裹有所述液滴的可凝胶化的溶液加入到凝固浴中的同时,使得所述凝固浴相对于出料口运动。
- 根据权利要求3所述的制备方法,其特征在于,在所述凝胶纤维形成同时对所述凝胶纤维进行拉伸。
- 根据权利要求1所述的制备方法,其特征在于,在形成所述液滴的同时通过可凝胶化的溶液包裹所述液滴。
- 根据权利要求6所述的聚合物粒子的制备方法,其特征在于,在形成所述液滴的同时通过可凝胶化的溶液包裹所述液滴,采用液滴形成包裹装置完成,所述液滴形成包裹装置,包括,用于放置含有功能性物料的聚合物溶液和/或反应性单体的第一腔;用于供所述可凝胶化的溶液流动的第二腔;所述第一腔与所述第二腔通过液滴形成孔联通。
- 根据权利要求6所述的制备方法,其特征在于,在形成所述液滴的同时通过可凝胶化的溶液包裹所述液滴,采用液滴形成包裹装置完成,所述液滴形成包裹装置,包括,用于供含有功能性物料的聚合物溶液和/或反应性单体流动的第一管路;套设在所述第一管路外,且与所述第一管路同轴,用于供所述可凝胶化的溶液流动的第二管路。
- 根据权利要求2所述的制备方法,其特征在于,功能性物料以非均相的状态包裹在聚合物溶液和/或反应性单体中的液滴,采用液滴形成包裹装置完成,所述液滴形成包裹装置,包括,用于供含有功能性物料的液体流动的第三管路;套设在所述第三管路外,且与所述第三管路同轴,用于供所述聚合物溶液和/或反应性单体流动的第四管路;套设在所述第四管路外,且与所述第四管路同轴,用于供所述可凝胶化的溶液流动的第五管路。
- 根据权利要求8或9所述的制备方法,其特征在于,在所述第二管路和第五管路的出口设置有导管。
- 根据权利要求1所述的制备方法,其特征在于,所述可凝胶化的溶液为离子敏感的体系溶液,或pH敏感的体系溶液,或温度敏感的溶液。
- 根据权利要求10所述的制备方法,其特征在于,所述离子敏感的体系溶液为,海藻酸钠溶液——多价盐溶液体系。
- 根据权利要求10所述的制备方法,其特征在于,所述pH敏感的体系溶液为,壳聚糖盐酸溶液——氢氧化钠溶液体系。
- 根据权利要求10所述的制备方法,其特征在于,所述温度敏感的溶液为泊洛沙姆溶液。
- 根据权利要求1所述的制备方法,其特征在于,所述功能性物料为,蛋白分子,或药物分子,或纳米粒子,或磁性粒子,或荧光染料,或香精,或香料,或制孔剂,或量子点中的一种或多种的组合。
- 根据权利要求1或15所述的制备方法,其特征在于,所述聚合物溶液为,聚乳酸—乙醇酸共聚物溶液,或聚乳酸溶液,或聚甲基丙烯酸甲酯溶液,或聚己内酯溶液中的一种或多种的组合;所述反应性单体为,或苯乙烯,或二乙烯苯,丙烯酸和甲基丙烯酸中的一种或多种的组合;所述可凝胶化的溶液为,海藻酸钠溶液——氯化钙溶液体系,或壳聚糖盐酸溶液——氢氧化钠溶液体系,或泊洛沙姆溶液;所述功能性物料为,蛋白分子,或药物分子,或纳米粒子,或磁性粒子,或荧光染料,或香精,或香料,或制孔剂,或量子点中的一种或多种的组合。
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CN1908257A (zh) * | 2006-08-16 | 2007-02-07 | 四川大学 | 一种原位胶囊化制备相变储能纤维的方法 |
CN104245114A (zh) * | 2012-01-31 | 2014-12-24 | 卡普苏姆公司 | 用于制备硬化的胶囊的方法 |
CN105175753A (zh) * | 2015-10-11 | 2015-12-23 | 中国海洋大学 | 一种单分散壳聚糖微球的制备方法和所用装置 |
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JPS61252202A (ja) * | 1985-05-01 | 1986-11-10 | Shiro Matsumoto | 均一な球状重合体の製造方法 |
WO2000018254A2 (en) * | 1998-09-25 | 2000-04-06 | Kemin Industries, Inc. | Method of protecting heat- or oxygen-labile compounds to preserve activity and bioavailability |
CN1908257A (zh) * | 2006-08-16 | 2007-02-07 | 四川大学 | 一种原位胶囊化制备相变储能纤维的方法 |
CN104245114A (zh) * | 2012-01-31 | 2014-12-24 | 卡普苏姆公司 | 用于制备硬化的胶囊的方法 |
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