Novel package for hydrolyzed sponge and preparation method

Abstract

The invention discloses a novel package for hydrolytic sponge and a preparation method thereof. The package comprises a carrier bone needle, the component of the carrier bone needle is silicon dioxide, the carrier bone needle is of a porous structure, the pore diameter range is 10-500 nm, and the porosity is not lower than 70%; the wrapping layer covers the outer surface of the bone needle, is synthesized by a biodegradable polymer and is added with a sebum response type plasticizer; by adopting a high-pressure pre-landfill process, liquid nutritional ingredients can be forcibly pressed into the deep positions of micro-pores of the silicon dioxide bone needle, meanwhile, by optimizing the material and the thickness of a wrapping layer, accurate regulation and control of active ingredient release kinetics are achieved, a continuous release window from several hours to more than ten hours can be provided, and the preparation process is simple and convenient. Therefore, long-acting nourishing on the skin is realized, the shortages of instant effect and non-lasting effect of traditional cosmetics are overcome, the high loading rate and deep filling far beyond those of a conventional adsorption method are realized, and the problems that active ingredients are easy to fall off and are released too fast due to the fact that the active ingredients are only attached to the surface of a carrier are solved.

Description

Technical Field

[0001] This invention relates to the field of cosmetic coating technology, and in particular to a novel coating method and preparation method for hydrolyzed sponges. Background Technology

[0002] Currently, adsorbent materials with high specific surface area, such as silica, porous glass, or activated carbon, are commonly used to load nutrients such as PDRN, peptides, or vitamins through physical adsorption or impregnation, and then add them to cosmetic formulations.

[0003] Conventional adsorption methods often fail to achieve high loading rates and deep filling, with active ingredients only adhering to the surface of the carrier or shallow pores. This results in rapid release and short duration of action in actual use. Furthermore, existing encapsulation layers often rely on water solubility or pH response mechanisms, making it difficult to achieve precise release behavior in the sebum environment. Especially in areas with high sebum secretion, such as the face, the release rate cannot match the skin's physiological state. In addition, some encapsulation materials have poor stability in cosmetic matrices, making them prone to early dissolution or peeling, which affects the product's shelf life and efficacy.

[0004] Therefore, in response to the problems mentioned above, this invention proposes a novel encapsulation and preparation method for hydrolyzed sponges. Summary of the Invention

[0005] To overcome the problems of low loading rate, mismatch between release behavior and skin environment, and insufficient stability of the encapsulation layer in cosmetic systems of existing carriers, this invention proposes a novel encapsulation and preparation method for hydrolyzed sponges. The method achieves efficient loading of nutrients in the pores of the bone needles through high-pressure process and uses a polymer encapsulation layer that is biodegradable in the sebum environment, thereby achieving slow and continuous release of active ingredients in the target area.

[0006] The technical solution of this invention is: a novel encapsulation for hydrolyzed sponges, comprising: The porous carrier bone needle is composed of silicon dioxide and has an interconnected network-like porous structure. The pore size distribution ranges from 10 to 500 nm, preferably 50 to 200 nm, the porosity is not less than 70%, preferably 75% to 90%, and the particle size ranges from 10 to 200 μm, preferably 20 to 80 μm, in order to adapt to the gaps in the stratum corneum of the skin. The specific surface area is 200 to 800 m² / g, preferably 400 to 600 m² / g. Liquid nutrients are loaded into the pores of the bone needle through a high-pressure pre-filling method. A sebum-responsive coating layer completely covers the outer surface of the loaded bone spur. The coating layer material includes a biodegradable polymer and a sebum-responsive plasticizer. The biodegradable polymer is selected from one or more of polylactic acid-glycolic acid copolymer (PLGA), polycaprolactone (PCL), and polylactic acid (PLA), preferably PLGA, with a monomer molar ratio of lactic acid to glycolic acid of 50:50 to 85:15. The sebum-responsive plasticizer is selected from one or more of monoglycerides, lecithin, and bile salts, and its mass percentage in the coating layer is 1%-10%, preferably 3%-6%. The thickness of the coating layer is 0.1-5μm, preferably 0.5-2μm, and the coefficient of variation of the thickness is not greater than 15%, so as to ensure the uniformity of the coating. The coating layer is insoluble in water and conventional oil phases of cosmetics at room temperature and can remain stable in cosmetic materials with pH 5.0-8.0 for no less than 24 months. After contacting human sebum (the main components are triglycerides, free fatty acids, wax esters, etc.), the coating layer can begin to soften and dissolve within 5-60 minutes, thereby realizing the slow and continuous release of nutrients pre-filled in the internal bone needles, and the release duration can reach 2-12 hours.

[0007] This invention proposes a novel method for preparing a coating for hydrolyzed sponges, comprising the following steps: S1. Dry the silica bone needles in a vacuum environment at 80-120℃ for 2-6 hours to completely remove moisture and adsorbents from the pores. Preferably, the dried bone needles can be immersed in a 1%-5% silane coupling agent ethanol solution for 0.5-2 hours, then centrifuged and cured at 80°C for 1 hour to achieve surface activation. S2. The pretreated bone needles are mixed with liquid nutrients at a mass ratio of 1:1 to 1:5 to form a uniform slurry. The slurry is transferred to a high-pressure reactor and maintained at a pressure of 50-200 MPa for 10-60 minutes. The high-pressure process adopts a programmed pressure increase mode. First, it is maintained at 50 MPa for 10 minutes, and then the pressure is increased to the target pressure of 100-150 MPa and maintained for 20-40 minutes. After high-pressure treatment, the pressure is released and the loaded bone needles are removed. They are then subjected to low-temperature vacuum drying below 40°C to remove free liquid from the surface non-embedded pores. S3. The loaded bone needles treated in S2 are placed in a fluidized bed coating equipment or spray dryer. The biodegradable polymer and sebum-responsive plasticizer are dissolved in an organic solvent to form a coating solution. The bone needles are sprayed and coated under the conditions of inlet temperature 40-70℃ and outlet temperature 30-50℃ until a uniform coating layer of the target thickness is formed. The organic solvent is selected from one or more of dichloromethane, ethyl acetate, or acetone, and the mass concentration of the polymer in the coating solution is 5% to 15%. S4. The coated bone needles are cured in an inert gas environment at 30-50°C for 2-6 hours. The inert gas is nitrogen or argon. After curing, the needles are sieved using a standard sieve to collect the final product within the target particle size range and then aseptically packaged.

[0008] Preferably, in step S2, the ambient temperature is controlled at 15-30°C to avoid the inactivation of heat-sensitive nutrients (such as PDRN) by high temperatures.

[0009] The beneficial effects of this invention are: 1. This invention employs a high-pressure pre-filling process to force liquid nutrients (such as PDRN) deep into the micropores of silica needles. Simultaneously, by optimizing the material and thickness of the encapsulation layer, it achieves precise control over the release kinetics of active ingredients, providing a continuous release window from several hours to over ten hours. This results in long-lasting skin nourishment, overcoming the shortcomings of traditional cosmetics that offer only immediate effects and lack long-lasting efficacy. It enhances user experience and product effectiveness, achieving a loading rate and deep filling far exceeding conventional adsorption methods. It also solves the problems of easy detachment and excessively rapid release caused by active ingredients merely adhering to the carrier surface.

[0010] 2. The sebum-responsive coating layer designed in this invention utilizes the synergistic effect of biodegradable polymers (such as PLGA) and sebum-responsive plasticizers to achieve precise and controllable release of active ingredients on the skin surface. The coating layer is stable under normal conditions, but can specifically dissolve after contact with sebum in the target area, thereby ensuring that nutrients are slowly and continuously released only at the site where they need to be acted upon, which greatly improves the targeting and efficacy of the product. Attached Figure Description

[0011] Figure 1 The diagram shown is a cross-sectional view of the present invention. Figure 2 The diagram shown illustrates the preparation process of this invention.

[0012] Explanation of the labels in the attached diagram: 1. Coating layer; 2. Effective nutrients. Detailed Implementation

[0013] To make the objectives, technical solutions, and advantages of the embodiments of the present invention clearer, the technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are some embodiments of the present invention, but not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0014] Please see Figure 1 The present invention provides an embodiment: a novel encapsulation for hydrolyzed sponges: In this embodiment, the porous carrier bone needle is made of silica, which has an interconnected three-dimensional network porous structure. This structure forms a huge specific surface area and pore volume. Its huge porosity provides physical space for adsorption and containment of sufficient liquid nutrients. By embedding active ingredients (such as PDRN) into its micropores, external environmental factors such as light and oxygen can be effectively isolated, maintaining its biological activity during storage. After the coating layer degrades, the porous structure of the bone needle can serve as a temporary reservoir, allowing the active ingredients to slowly diffuse to the skin through the concentration gradient, rather than being released instantaneously.

[0015] In this embodiment, conventional atmospheric pressure soaking or stirring adsorption can only adsorb active ingredients onto the macropores and surface of the bone needle, and cannot effectively penetrate into the finer mesopores and some macropores. This invention solves this problem by using a high-pressure pre-filling process. By using ultra-high pressure (50-200MPa), the low-viscosity liquid nutrients are forced to overcome surface tension and capillary resistance, and quickly and deeply penetrate and fill the entire pore network of the bone needle.

[0016] This method can increase the loading rate from 10-20% in the atmospheric pressure method to 30%-50% or even higher, while allowing the active ingredients to be evenly distributed in the pores from the surface to the core, thus avoiding the burst release effect.

[0017] In this embodiment, the sebum-responsive coating uses a biodegradable polymer (such as PLGA) as the film-forming matrix. Its degradation rate can be adjusted by the monomer ratio (lactic acid:glycolic acid); a higher lactic acid ratio results in stronger hydrophobicity and slower degradation. A sebum-responsive plasticizer (such as lecithin) is added internally. Lecithin is an amphiphilic molecule with good compatibility with components such as triglycerides and fatty acids in sebum. When the coating comes into contact with sebum, the plasticizer interacts with the sebum, weakening the intermolecular forces between polymer chains and promoting the penetration of sebum components into the coating, thereby accelerating the swelling, softening, and eventual degradation of the polymer.

[0018] The polymer layer is insoluble in water-based or oil-based cosmetic systems at room temperature, ensuring the product's stability during its shelf life. It also degrades only upon contact with skin containing sebum, allowing for on-demand release and significantly improving ingredient utilization.

[0019] Please see Figure 2 The present invention provides an embodiment 1: Raw materials: silica bone needles (pore size 50-200nm, porosity 85%, particle size 50±10μm, specific surface area 550㎡ / g), PDRN solution (concentration 2mg / mL, solvent is a mixture of water and propylene glycol), PLGA (lactic acid:glycolic acid = 75:25), lecithin (purity >98%), dichloromethane, anhydrous ethanol, 3-aminopropyltriethoxysilane.

[0020] Preparation process: S1. Take 10 grams of silica bone needles and place them in a vacuum drying oven at 105°C for 4 hours to thoroughly remove the adsorbed moisture and volatile impurities in their pores. Then, immerse the dried bone needles in a 3% 3-aminopropyltriethoxysilane ethanol solution and gently stir at room temperature for 1 hour to complete the silanization reaction. Then, recover the bone needles by centrifugation and wash them twice with anhydrous ethanol to remove the physically adsorbed coupling agent. Finally, place the bone needles in an oven at 80°C for 1 hour to cure them, so that the coupling agent forms a stable chemical bond with the surface of the bone needles, thereby obtaining activated bone needles with amino functional groups on the surface.

[0021] S2, 5 grams of activated bone needles were mixed with 25 grams of PDRN solution with a concentration of 2 mg / ml (bone needle to solution mass ratio of 1:5) in a beaker and stirred to form a uniform suspension slurry. The slurry was then transferred to a high-pressure reactor and subjected to high-pressure treatment using a programmed pressurization mode. First, the pressure was maintained at 50 MPa for 10 minutes to initially compact the slurry and remove most of the gas. Then, the pressure was increased to 120 MPa at a rate of 10 MPa per minute and maintained at the target pressure for 30 minutes. The entire high-pressure process was carried out in a constant temperature water bath at 25°C to prevent the heat-sensitive PDRN from being deactivated. After the high-pressure treatment was completed, the pressure was slowly released, the slurry was removed, and wet bone needles loaded with PDRN were obtained by vacuum filtration. Finally, the slurry was placed in a vacuum drying oven at 35°C and dried overnight to remove free moisture from the surface and shallow pores, ultimately obtaining PDRN-loaded bone needles.

[0022] S3. First, prepare the coating solution by dissolving 1.5 g of PLGA (75:25 molar ratio of lactic acid to glycolic acid) and 0.075 g of lecithin (5% of the PLGA mass) as a sebum-responsive plasticizer in 13.5 g of dichloromethane. Stir until the polymer and plasticizer are completely dissolved to form a homogeneous and transparent coating solution. Then, load 5 g of PDRN-loaded bone needles obtained in step S2 into the material tank of a fluidized bed coating machine. Set the equipment inlet temperature to 55°C and the fluidizing air volume to 30 m³ / h. 3 With an atomization pressure of 0.3 MPa, the equipment is started to allow the bone needles to form a stable fluidized state under the action of airflow. After the bed temperature stabilizes, the coating solution is atomized through the nozzle and sprayed onto the surface of the fluidized bone needles at a constant rate of 2 ml per minute. The spraying process continues until the solution is completely sprayed. Then, hot air is continued to be introduced for drying for 15 minutes while maintaining fluidization, so that the organic solvent can be completely evaporated, thereby forming a uniform polymer coating layer on the surface of each loaded bone needle.

[0023] S4. The preliminary product obtained after fluidized bed coating is transferred to a sealed curing chamber filled with high-purity nitrogen and subjected to thermosetting treatment at 40°C for 4 hours under an inert atmosphere. After curing, the product is removed and sieved using a 200-mesh standard sieve to remove excessively large particles that may have formed due to agglomeration or fine powder that may have been broken. Finally, the final product with a specified particle size range that passes through the sieve is collected and sealed and packaged in a light-proof container for use in subsequent cosmetic formulations. This product is named "Sample A".

[0024] This invention provides an embodiment 2: Raw materials: silica bone needles (pore size 50-200nm, porosity 85%, particle size 50±10μm, specific surface area 550 m² / g), nicotinamide (5% aqueous solution), arbutin (3% aqueous solution), polycaprolactone (PCL, molecular weight 50,000), glycerol monoester (purity >90%), dichloromethane, anhydrous ethanol, 3-aminopropyltriethoxysilane.

[0025] Preparation process: S1. Take 10 grams of silica bone needles and place them in a vacuum drying oven at 105°C for 4 hours to completely remove moisture from the pores. Then, immerse the dried bone needles in a 3% APTES ethanol solution and gently stir at room temperature for 1 hour. Then, recover the bone needles by centrifugation and wash them twice with anhydrous ethanol. Finally, cure them in an 80°C oven for 1 hour to allow the coupling agent to stably bond with the surface of the bone needles, thus obtaining surface-activated bone needles.

[0026] S2, 5 grams of activated bone needles were mixed with 25 grams of a mixed solution of nicotinamide and arbutin (mass ratio 1:5) in a beaker to form a uniform slurry. The slurry was transferred to a high-pressure reactor and maintained at a constant pressure of 100 MPa for 40 minutes. The entire process was carried out in a constant temperature water bath at 25°C to prevent component decomposition. After high-pressure treatment, the pressure was slowly released, and the slurry was taken out and separated by vacuum filtration to obtain wet bone needles loaded with whitening ingredients. Finally, it was placed in a vacuum drying oven at 35°C and dried overnight to obtain high-load bone needles.

[0027] S3. First, prepare the coating solution by dissolving 1.5 g of PCL and 0.06 g of monoglyceride (4% of the mass of PCL) in 13.5 g of dichloromethane and stirring to form a homogeneous solution. Then, 5 g of loaded bone needles and an appropriate amount of dispersant are placed in water to form a suspension. The suspension is then delivered to the spray dryer at a rate of 10 mL / min using a peristaltic pump. The inlet temperature is set to 60 °C, the outlet temperature to 40 °C, and the atomization pressure to 0.4 MPa, so that the atomized droplets can fully contact the bone needles to form a uniform coating layer.

[0028] S4. Transfer the spray-dried product to a curing chamber filled with high-purity nitrogen and cure it at 40°C for 4 hours to enhance the density of the coating layer. After curing, use a 200-mesh sieve to sieve the product. Collect the final product that passes through the sieve and seal it for storage in the dark. Name it "Sample B".

[0029] This invention provides an embodiment 3: Raw materials: silica bone needles (pore size 50-200nm, porosity 85%, particle size 50±10μm, specific surface area 550㎡ / g), PDRN solution (concentration 2mg / mL, solvent is a mixture of water and propylene glycol), PLGA (lactic acid: glycolic acid = 50:50), lecithin (purity >98%), dichloromethane, anhydrous ethanol, 3-aminopropyltriethoxysilane.

[0030] S1. Take 10 grams of silica bone needles and place them in a vacuum drying oven at 105°C for 4 hours to thoroughly remove moisture and impurities from the pores. Then, immerse the dried bone needles in a 3% APTES ethanol solution and gently stir at room temperature for 1 hour to complete the silanization reaction. Then, recover the bone needles by centrifugation and wash them twice with anhydrous ethanol to remove unreacted coupling agent. Finally, place the bone needles in an oven at 80°C for 1 hour to cure them so that the coupling agent forms a stable chemical bond with the surface of the bone needles, thus obtaining surface-activated bone needles.

[0031] S2, 5g of activated bone needles and 25g of PDRN solution were mixed in a beaker at a mass ratio of 1:5 and mechanically stirred to form a uniform slurry. The slurry was transferred to a high-pressure reactor and pressurized at 50MPa for 10 minutes using a programmed pressurization mode. Then, the pressure was increased to 120MPa at a rate of 10MPa / min and maintained for 30 minutes. The entire process was carried out in a constant temperature water bath at 25℃. After the high-pressure treatment was completed, the pressure was slowly released, and the slurry was removed and filtered to obtain wet bone needles loaded with PDRN. Finally, the slurry was placed in a vacuum drying oven at 35℃ and dried overnight to obtain PDRN-loaded bone needles.

[0032] S3. First, prepare the coating solution by dissolving 0.75 g of PLGA (50:50 molar ratio of lactic acid to glycolic acid) and 0.0375 g of lecithin in 13.5 g of dichloromethane and stirring to form a homogeneous coating solution. Then, load 5 g of PDRN-loaded bone needles into a fluidized bed coating machine, setting the inlet temperature to 55℃ and the fluidizing air volume to 30 m³ / h. 3 At a speed of 1 ml / min and an atomization pressure of 0.3 MPa, the equipment is started to form a stable fluidized state for the bone needle. The coating solution is then sprayed at a rate of 1 ml / min and the final coating thickness is controlled by real-time monitoring to be 0.5 ± 0.1 micrometers. After spraying, the solution is dried for 15 minutes while maintaining fluidization to allow the solvent to evaporate completely.

[0033] S4. The coated bone needles are transferred to a curing chamber filled with high-purity nitrogen and cured at 40°C for 3 hours to enhance the stability of the thin-layer coating and avoid excessive polymer degradation. After curing, a 200-mesh standard sieve is used to remove any agglomerated particles. The final product with uniform particle size that passes through the sieve is collected, sealed and protected from light, and named "Sample C".

[0034] This invention provides a comparative example: (1) The present invention provides a comparative group for comparison with the present invention. In comparative group 1, the unmodified bone needles were directly immersed in PDRN solution (bone needle: solution = 1:5), stirred at normal pressure for 12 hours, filtered and dried. The resulting sample had no coating layer. In comparative group 2, PDRN-loaded bone needles were prepared using the same method as in Example 1, but the coating layer was only PLGA (lactic acid: glycolic acid = 75:25), and no lecithin was added.

[0035] Weigh a certain mass of samples A, B, C and Comparative Example 1, dissolve the coating layer with an organic solvent (such as acetone), and then use an appropriate solvent to completely extract the active ingredients from the pores of the bone needles. The content of the active ingredients is determined by HPLC.

[0036]

[0037] As shown in the table above, the high-pressure pre-filling process of the present invention (samples A and C) has a loading rate that is about 2.7 times higher than that of the atmospheric pressure adsorption method (comparative example 1), which proves that the high-pressure method has great advantages in terms of deep filling and high loading.

[0038] (2) The dialysis bag method was used to simulate the sebum environment. The release medium was PBS buffer (pH=5.5) containing 5% Tween 80 and 1.5% free fatty acids to simulate facial sebum. The sample was placed in a dialysis bag and shaken at 100 rpm at 37°C. Samples were taken at predetermined time points, and an equal amount of fresh medium was added at the same temperature. The amount of released active ingredients was determined by HPLC, and the cumulative release rate was calculated.

[0039]

[0040] As shown in the table above, sample A releases approximately 15% within 0-2 hours (initial release of a small amount of surface residual components), and then enters a stable sustained-release platform, accumulating to over 85% release within 12 hours. This indicates that the coating layer begins to degrade upon encountering simulated sebum, triggering the continuous release of internal components.

[0041] Sample C released significantly faster, with about 30% released within 2 hours and more than 90% released within 8 hours, demonstrating that the release rate can be flexibly controlled by adjusting the coating thickness and polymer type.

[0042] Comparative Example 1 showed that more than 90% of the sample was released within 1 hour, exhibiting a typical burst release phenomenon.

[0043] Comparative Example 2 showed a cumulative release rate of only about 25% within 12 hours, indicating that in the absence of sebum-responsive plasticizers, the PLGA encapsulation layer degrades very slowly in the simulated sebum environment, failing to effectively release the active ingredients.

[0044] (3) Sample A and Comparative Example 1 were added to a water-based serum formulation and placed in an accelerated stability test chamber at 40℃±2℃ and 75%±5%RH. Samples were taken after 0, 1, 2 and 3 months to determine the activity retention rate of PDRN (evaluated by HPLC peak area and cell activity experiment).

[0045]

[0046] As shown in the table above, the encapsulation layer in sample A protects the internal PDRN, enabling it to maintain more than 94% of its activity after 3 months under accelerated conditions. In contrast, due to the lack of protection, the PDRN in Comparative Example 1 was directly exposed to the formulation environment, resulting in significant degradation and a substantial decrease in activity. This demonstrates the excellent protective ability of the encapsulation structure of the present invention for sensitive active ingredients.

[0047] The above are merely preferred embodiments of the present invention and are not intended to limit the present invention in any other way. Any person skilled in the art may make changes or modifications to the above-disclosed technical content to create equivalent embodiments that can be applied to other fields. However, any simple modifications, equivalent changes, and modifications made to the above embodiments based on the technical essence of the present invention without departing from the scope of the present invention shall still fall within the protection scope of the present invention.

Claims

1. A novel encapsulation method for hydrolyzed sponges, characterized in that, Including: The carrier bone needle is made of silica and has a porous structure with a pore size range of 10-500 nm and a porosity of not less than 70%. The bone needle is pre-filled with liquid nutrients into its micropores through high-pressure pretreatment. The encapsulation layer, covering the outer surface of the bone spur, is synthesized from a biodegradable polymer, wherein the biodegradable polymer is selected from at least one of polylactic acid-glycolic acid copolymer, polycaprolactone, and polylactic acid, and contains a sebum-responsive plasticizer. The coating layer is insoluble in water at room temperature and can exist stably in cosmetic materials. The coating layer can gradually degrade or dissolve after contact with human sebum.

2. The novel encapsulation method for hydrolyzed sponges according to claim 1, characterized in that: The liquid nutrients include at least one of PDRN, polypeptides, amino acids, vitamins, and plant extracts.

3. A novel encapsulation method for hydrolyzed sponges according to claim 1, characterized in that: The sebum-responsive plasticizer is at least one of monoglycerides, lecithin, and bile salts, and its mass percentage in the coating layer is 1%-10%.

4. A novel encapsulation method for hydrolyzed sponges according to claim 1, characterized in that: The coating layer has a thickness of 0.1-5 μm and is uniformly applied to the surface of the bone needle.

5. A novel encapsulation method for hydrolyzed sponges according to claim 1, characterized in that: The bone needles have a particle size range of 10-200 μm and a specific surface area of ​​200-800 m² / g.

6. A method for preparing a novel encapsulation for hydrolyzed sponges, based on the novel encapsulation for hydrolyzed sponges according to any one of claims 1-5, characterized in that, It includes the following steps: S1, Dry the silica bone needles under vacuum conditions to remove moisture and impurities; S2, mix the liquid nutrients with the bone needles, place them in a high-pressure reactor, and maintain the pressure at 50-200MPa for 10-60 minutes to allow the nutrients to fully penetrate into the pores of the bone needles; S3, the bone needles treated in step S2 are immersed in a solution containing biodegradable polymers and sebum-responsive plasticizers, and a uniform coating layer is formed by spray drying or fluidized bed coating process; S4, the coating layer is cured at 30-50℃, and the finished product is collected by sieving.

7. The method for preparing a novel encapsulation for hydrolyzed sponges according to claim 1, characterized in that: In step S2, the pressure is preferably 100-150 MPa and the time is 20-40 minutes.

8. The method for preparing a novel encapsulation for hydrolyzed sponges according to claim 1, characterized in that: In step S3, the solution is a solution of PLGA dissolved in dichloromethane or ethyl acetate, with a concentration of 5%-15%.

9. The method for preparing a novel encapsulation for hydrolyzed sponges according to claim 1, characterized in that: The inlet temperature of the spray dryer is 40-70℃, and the outlet temperature is 30-50℃.

10. The method for preparing a novel encapsulation for hydrolyzed sponges according to claim 1, characterized in that: Step S4 is performed under inert gas protection to prevent oxidation or degradation of the coating layer.

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