A hydrocolloid dressing for ostomy pouches and its use
Hydrocolloid dressings prepared through specific formulations and segmented processes have solved the problem of unstable adhesion of hydrocolloid dressings in wet environments, achieving high initial tack and tack retention in humid environments, reducing the risk of leakage and skin irritation, and improving user comfort.
Patent Information
- Authority / Receiving Office
- CN · China
- Patent Type
- Applications(China)
- Current Assignee / Owner
- XIAMEN PUBO MEDICAL TECH CO LTD
- Filing Date
- 2026-03-30
- Publication Date
- 2026-06-02
AI Technical Summary
Existing hydrocolloid dressings struggle to balance initial tack with long-term tack, as well as tack retention and comfort in wet environments. They are particularly prone to loosening, leakage, or skin irritation in damp, seepage-prone conditions.
Pressure-sensitive adhesives with specific formulations, including polymer colloids, polyisobutylene compositions, tackifying resins, glycerin, sodium carboxymethyl cellulose, and affinity block copolymers, are used to prepare hydrocolloid dressings through a segmented process. This process forms a stable cohesive network and complementary microphase structure, improving initial tack, holding power, and water management capabilities.
It achieves an optimal balance between initial tack, holding power, wet tack, water absorption management, and skin compatibility, improving rapid adhesion in humid environments, reducing the risk of leakage and skin irritation, and enhancing wearing comfort and adhesion reliability.
Smart Images
Figure CN122124313A_ABST
Abstract
Description
Technical Field
[0001] This invention relates to the field of medical dressing technology, and more specifically, to a hydrocolloid dressing for an adhesive base plate of an ostomy bag and its application. Background Technology
[0002] The adhesive base of the ostomy bag places high demands on the dressing's adhesion, breathability, absorbency, re-adhesion capability, and skin compatibility. In existing technologies, common hydrocolloid dressings often struggle to achieve a balance between initial tack and long-term tack, as well as adhesion retention and comfort in humid environments. Furthermore, prolonged wear or exposure to moisture can lead to loosening, leakage, or skin irritation. Especially in moist, exudative environments, they fail to adhere well to the skin. Traditional hydrophobic pressure-sensitive adhesives show a significant decrease in adhesion upon contact with interfacial moisture, easily resulting in leakage or detachment. Some formulations have weak absorbency, failing to effectively manage trace amounts of exudate or sweat around the stoma, leading to skin maceration, redness, or irritation with prolonged wear. Summary of the Invention
[0003] In view of this, the object of the present invention is to provide a hydrocolloid dressing for an adhesive base plate of an ostomy bag and its application therein, so as to solve the above problems.
[0004] The present invention adopts the following solution: This application provides a hydrocolloid dressing for an ostomy bag adhesive baseplate, composed of a pressure-sensitive adhesive; the raw materials of the pressure-sensitive adhesive include the following components in parts by weight: 24 parts polymer colloid, 42 parts polyisobutylene composition, 3 parts tackifying resin, 6 parts glycerol, 15 parts sodium carboxymethyl cellulose, and 10 parts affinity block copolymer; the polyisobutylene composition is high molecular weight polyisobutylene and low molecular weight polyisobutylene; the affinity block copolymer is polyethylene glycol and polyglycerol decanoate; The preparation method of this hydrocolloid dressing includes the following steps: S1: The polymer colloid, tackifying resin, and glycerin are sequentially added to the thermal dispersion treatment and heated and stirred. S2: While stirring, mix in the polyisobutylene composition formulated with high molecular weight polyisobutylene and low molecular weight polyisobutylene. After stirring and mixing evenly, a continuous phase pressure-sensitive adhesive is obtained. S3: Perform vacuuming, then cool down, and continue adding sodium carboxymethyl cellulose to the continuous phase pressure-sensitive adhesive while stirring; S4: Continuously heat and stir, and simultaneously mix polyethylene glycol and polyglycerol decanoate to prepare a pressure-sensitive adhesive; S5: Apply the pressure-sensitive adhesive to the adhesive base to obtain the hydrocolloid dressing.
[0005] As a further improvement, in step S2, the mixing temperature is 120°C to 125°C, the mixing time is 60 min to 65 min, and the stirring speed is 60 r / min to 65 r / min.
[0006] As a further improvement, in step S3, the temperature after cooling is 90°C to 100°C, and the stirring speed is 20 r / min to 30 r / min.
[0007] As a further improvement, in step S4, the mixing time is 80 min to 90 min, and the mixing temperature and stirring speed are consistent with those in step S2.
[0008] As a further improvement, the high molecular weight polyisobutylene is 32 parts, and the low molecular weight polyisobutylene is 10 parts, and the molecular weight of the low molecular weight polyisobutylene is less than 1000.
[0009] As a further improvement, the polyethylene glycol is 2 parts and the polyglycerol decanoate is 8 parts; the polyethylene glycol is a hydrophilic material used to absorb interfacial moisture; the polyglycerol decanoate is a hydrophobic material used to provide viscoelasticity.
[0010] As a further improvement, the polymer colloid is a continuous phase colloid and contains at least zinc oxide powder and polyurethane.
[0011] As a further improvement, the polymer colloid is an acrylate copolymer configured as a triblock structure consisting of styrene-isoprene-styrene.
[0012] As a further improvement, in step S1, the thermal dispersion treatment is performed by a heated disperser device for providing the raw materials of the pressure-sensitive adhesive to the reaction vessel for stirring and mixing.
[0013] In addition, this application also provides the application of hydrocolloid dressings as medical dressings.
[0014] By adopting the above technical solution, the present invention can achieve the following technical effects: 1. The hydrocolloid dressing for ostomy bag adhesive baseplate of this application achieves an optimal balance between initial tack, holding power, wet tack, absorbency management, and skin compatibility through the synergistic design of the formulation and segmented process. This satisfies the comprehensive requirements of ostomy bag adhesive baseplate for long-term adhesion, leak resistance, and gentleness to the skin around the stoma. In particular, the tackifying resin and the affinity block copolymer in the formulation synergistically improve the wettability and interfacial fluidity of the system at the moment of contact, enhance the rapid adhesion ability in a humid environment, thereby improving the initial adhesion rate and initial tack. Furthermore, the affinity block copolymer and the polymer colloid can synergistically provide more efficient holding performance and ensure that there is little residue when peeling off. This makes it easy for users to quickly stick, position, and fix the dressing, reducing secondary adjustments, maintaining adhesive strength, and removing the adhesive when peeling off.
[0015] 2. The polymer colloid (such as SIS-type acrylate copolymer) forms a stable cohesive network with high molecular weight polyisobutylene, providing durable cohesive strength and elastic recovery. It is not easy to loosen under gravity, friction or continuous tensile force, reducing the risk of ostomy bag falling off and leakage during long-term wear.
[0016] 3. Polyethylene glycol (PEG) in the affinity block copolymer provides hydrophilic absorption sites to absorb interfacial moisture, while the hydrophobic segments of polyglycerol decanoate maintain viscoelasticity, enabling the adhesive layer to maintain a certain mechanical bonding function in a wet state. This inhibits water damage to the bonding interface and maintains high bonding reliability even under conditions of sweating or localized seepage, reducing wet detachment and leakage.
[0017] 4. Sodium carboxymethyl cellulose (CMCNa) swells in the presence of water to form a local gel structure, which disperses or retains exudate. At the same time, it works synergistically with PEG to improve water distribution and drainage, reduce the risk of skin maceration, friction irritation and ulceration around the stoma, and improve the comfort and skin protection of long-term wear.
[0018] 5. The SIS triblock / acrylate matrix provides the system with thermal stability and mechanical resilience. The ratio of tackifying resin to glycerol can be designed to adjust the thermal processing performance and post-curing flexibility, thereby reducing the mechanical property degradation caused by storage / aging. The product has good shelf life and transportation / storage stability, which is convenient for industrial-scale production and quality control.
[0019] 6. By segmented feeding and limiting temperature and rotation speed, the protection of heat-sensitive components, controllable phase distribution, and suppression of bubbles are ensured. The final coating can be done using existing doctor blade or tank coating equipment. The process is easy to scale up, has good consistency, controllable quality, and is feasible for industrial production. Attached Figure Description
[0020] Figure 1This is a flowchart of a method for preparing a hydrocolloid dressing for an ostomy bag adhesive baseplate according to an embodiment of the present invention. Figure 2 This is a schematic diagram illustrating an application scenario of hydrocolloid dressing for an ostomy bag adhesive base plate according to an embodiment of the present invention; Figure 3 This is a line diagram illustrating the initial tack / holding tack of various embodiments and comparative examples of the hydrocolloid dressing for the adhesive base of the ostomy bag according to the present invention at each time period. Detailed Implementation
[0021] 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 only some, not all, of the embodiments of the present invention. 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. Therefore, the following detailed description of the embodiments of the present invention provided in the accompanying drawings is not intended to limit the scope of the claimed invention, but merely to illustrate selected embodiments of the invention. Example
[0022] Combination Figures 1 to 3 This embodiment provides a hydrocolloid dressing for an ostomy bag adhesive baseplate, composed of a pressure-sensitive adhesive. The pressure-sensitive adhesive comprises the following components by weight: 24 parts polymer colloid, 42 parts polyisobutylene composition, 3 parts tackifying resin, 6 parts glycerol, 15 parts sodium carboxymethyl cellulose, and 10 parts affinity block copolymer. The polyisobutylene composition is composed of high molecular weight polyisobutylene and low molecular weight polyisobutylene. The affinity block copolymer is composed of polyethylene glycol and polyglycerol decanoate.
[0023] The preparation method of this hydrocolloid dressing includes the following steps: S1: The polymer colloid, tackifying resin, and glycerin are sequentially added to the thermal dispersion treatment and heated and stirred. S2: While stirring, mix in the polyisobutylene composition formulated with high molecular weight polyisobutylene and low molecular weight polyisobutylene. After stirring and mixing evenly, a continuous phase pressure-sensitive adhesive is obtained. S3: Perform vacuuming, then cool down, and continue adding sodium carboxymethyl cellulose to the continuous phase pressure-sensitive adhesive while stirring; S4: Continuously heat and stir, and simultaneously mix polyethylene glycol and polyglycerol decanoate to prepare a pressure-sensitive adhesive; S5: Apply the pressure-sensitive adhesive to the adhesive base to obtain the hydrocolloid dressing.
[0024] The hydrocolloid dressing for ostomy bag adhesive baseplates described above achieves an optimal balance between initial tack, holding power, wet tack, absorbency management, and skin compatibility through synergistic design of the formulation and segmented process. This satisfies the comprehensive requirements of ostomy bag adhesive baseplates for long-term adhesion, leak resistance, and gentleness on the skin around the stoma. In particular, the tackifying resin and affinity block copolymer in the formulation synergistically improve the wettability and interfacial flowability of the system upon contact, enhancing rapid adhesion in humid environments, thereby increasing the initial adhesion rate and initial tack. Furthermore, the affinity block copolymer and polymer colloid synergistically provide more efficient holding performance and ensure minimal residue upon peeling. This allows for easy and quick application, positioning, and fixation by the user, reducing secondary adjustments, maintaining adhesive strength, and facilitating easy removal of adhesive residue upon peeling.
[0025] Furthermore, the polymer colloid (such as SIS-type acrylate copolymers) forms a stable cohesive network with high molecular weight polyisobutylene, providing durable cohesive strength and elastic recovery. It is not easily loosened under gravity, friction, or continuous tensile force, reducing the risk of ostomy bag detachment and leakage during long-term wear. Polyethylene glycol (PEG) in the hydrophilic block copolymer provides hydrophilic absorption sites, absorbing interfacial moisture, while the hydrophobic segment of polyglycerol decanoate maintains viscoelasticity, allowing the adhesive layer to maintain a certain degree of mechanical adhesion even in a wet state. This inhibits water damage to the adhesive interface, maintaining high adhesive reliability even under sweating or localized exudation, reducing wet detachment and leakage. Sodium carboxymethyl cellulose (CMCNa) swells in the presence of water to form a localized gel structure, dispersing or retaining exudate. Simultaneously, it synergistically works with PEG to improve moisture distribution and drainage, reducing the risk of peristomal skin maceration, friction irritation, and ulceration, and improving comfort and skin protection during long-term wear. The hydrophilicity of PEG and CMCNa, along with the currently selected modified non-toxic fillers (such as trace amounts of ZnO and medical-grade polyurethane), helps reduce skin irritation. At the same time, the formulation and process avoid or reduce harmful volatile components, reducing the risk of skin allergies / irritation, making it suitable for long-term medical applications applied to the skin around the stoma.
[0026] In particular, the segmented feeding and the limitation of temperature and rotation speed ensure the protection of heat-sensitive components, controllable phase distribution, and suppression of bubbles. The final coating can be applied using existing doctor blade or tank coating equipment. The process is easy to scale up, has good consistency, and controllable quality, making industrial production feasible. Details are as follows: In step S2, the mixing temperature is 120°C to 125°C, the mixing time is 60 min to 65 min, and the stirring speed is 60 r / min to 65 r / min. This temperature range is sufficient to allow the acrylate copolymer, tackifying resin, and glycerol to fully swell, reduce the system viscosity, and facilitate thorough miscibility with high / low molecular weight PIB. A preferred continuous stirring time of 65 min ensures that the low molecular weight PIB is uniformly dispersed in the continuous phase and fully wets the skin interface components. This avoids phase separation due to excessively short mixing or the risk of thermal oxidation due to excessively long mixing. The moderate stirring speed of 65 r / min provides sufficient shear at high temperatures to disperse the components without generating excessive bubbles or shear degradation. This results in a uniform, continuous pressure-sensitive adhesive phase, improving cohesive strength and shear retention, and enhancing initial tack and wettability (low molecular weight PIB provides surface wetting), facilitating rapid bonding and positioning. The stable system viscosity promotes consistent coating thickness and improves industrial repeatability.
[0027] In step S3, the temperature after cooling is 90℃ to 100℃, and the stirring speed is 20 r / min to 30 r / min. Cooling protects heat-sensitive components (such as CMCNa and PEG) from high-temperature degradation, while simultaneously increasing the system viscosity to a range favorable for solid-phase dispersion. The low stirring speed during the cooling stage avoids strong shearing that could cause fibrosis or damage to the dispersibility of water-soluble polymers, and facilitates the rise and escape of bubbles during vacuuming. Vacuuming first eliminates dissolved gases and entrained microbubbles generated during mixing, improving coating density. Thus, CMCNa achieves uniform dispersion under milder conditions, exerting its water-absorbing / gelling function, reducing microbubbles and voids, minimizing coating defects, improving the appearance and mechanical uniformity of the finished product, enhancing interfacial stability in a wet state, and facilitating the subsequent controllable formation of hydrophilic / hydrophobic phases.
[0028] In step S4, the mixing time is 80 to 90 minutes, and the mixing temperature and stirring speed are consistent with those in step S2. Mixing for a longer time under relatively stable low-speed stirring conditions allows the hydrophilic block copolymer (PEG / polyglycerol decanoate) to complete interdiffusion and self-assembly within the continuous phase, forming the desired hydrophilic and hydrophobic microstructures. Furthermore, the same stirring rate and mixing temperature as in S2 ensure the consistency of the final system under shear conditions, thereby forming repeatable microstructures and macroscopic rheological properties. This results in a stable hydrophilic / hydrophobic complementary microphase structure, significantly improving tack retention and water absorption management after immersion in water, ultimately achieving a good balance between initial tack, viscoelasticity, and long-term aging stability of the pressure-sensitive adhesive.
[0029] Preferably, the high molecular weight polyisobutylene (PIB) comprises 32 parts, and the low molecular weight polyisobutylene (PIB) comprises 10 parts, with the low molecular weight PIB having a molecular weight below 1000. Clearly, low molecular weight PIB (Mw < 1000) has short molecular chains and low viscosity, making it easy to flow upon contact and wet the microscopic rough structure of the skin surface, thus quickly forming a contact area and improving initial adhesion. This makes it easier for the user to position the dressing and achieve rapid adhesion, reducing the probability of secondary adjustments and slippage. High molecular weight PIB, on the other hand, has long chains and more intermolecular entanglement, providing a cohesive framework for the adhesive layer, improving shear resistance and anti-flow ability. Under continuous load or friction, the dressing is less prone to material flow or peeling, meeting the requirements for long-term wear of ostomy bags. In particular, the high molecular weight polyisobutylene with a high proportion of low Mw components provides surface wetting and instant adhesion, while the high Mw components provide cohesion and structural support. The two complement each other at the microscopic level, which avoids the cold flow caused by low Mw alone and the insufficient initial tack caused by high Mw alone. This achieves comprehensive performance with high initial tack and high shear retention, reducing the use risks caused by the rheological properties of the material itself.
[0030] In this embodiment, the polyethylene glycol (PEG) comprises 2 parts, and the polyglycerol decanoate (PGDA) comprises 8 parts. PEG is a hydrophilic material used to absorb interfacial moisture. PGDA is a hydrophobic material used to provide viscoelasticity. The combination of 2 parts PEG and 8 parts PGDA achieves a quantitative balance between the hydrophilic and hydrophobic phases. The hydrophilic portion is sufficient to handle trace amounts of interfacial moisture, while the hydrophobic portion is sufficient to maintain overall mechanical and adhesive properties. The two phases form a complementary microstructure, thereby significantly improving the adhesion retention after immersion in water while maintaining both initial tack and holding power.
[0031] In this embodiment, the polymer colloid is a continuous phase colloid, and at least zinc oxide powder and polyurethane are added. On one hand, the zinc oxide powder (ZnO) micro-nano particles are uniformly dispersed in the continuous phase, providing mild antimicrobial activity and an antibacterial environment through physical contact and microenvironment regulation. Simultaneously, it participates in stress transfer as an inorganic filler, increasing the material's rigidity and wear resistance. On the other hand, the polyurethane (PU) is a polymeric elastomer or thermoplastic polyurethane, which can form a flexible network or intertwined structure within the continuous phase, improving the material's elongation at break and fracture toughness. The synergistic dispersion structure of both in the continuous phase helps to significantly improve the reliability and skin mechanical adaptability of the hydrocolloid dressing under long-term wear, repeated bending, and humid environments without compromising the hydrophilic and hydrophobic microphase structure.
[0032] In another embodiment, the polymer colloid is an acrylate copolymer configured as a triblock structure of styrene-isoprene-styrene. Specifically, the SIS triblock material forms a phase-separated structure at the microscopic level between a rigid styrene hard phase and a flexible isoprene / acrylate soft phase. The styrene hard phase acts as a physical crosslinking point, providing excellent cohesive strength and tear resistance to the pressure-sensitive adhesive, while the isoprene / acrylate soft phase imparts the necessary elasticity and wetting ability to the adhesive layer. This further exhibits a good balance between initial tack and holding tack, aging resistance, and industrial processing adaptability, thereby improving the long-term wearing reliability and comfort of the ostomy bag adhesive baseplate. Specifically, this triblock structure does not contain plasticizers and possesses excellent transparency, weather resistance, hydrolysis resistance, low-temperature flexibility, and high flowability, enabling good compatibility with highly polar materials.
[0033] In other embodiments, the polymer colloid is a triblock structure system composed of a base polymer, compound components, and modifiers. This triblock structure preferably comprises a block distribution of hard segments, soft segments, and more hard segments, wherein the hard segments preferably comprise polymethyl methacrylate (PMMA) segments, and the soft segments are preferably elastic rubbery segments (e.g., isoprene or acrylate segments). In this triblock structure, the PMMA segment content is typically 30% (by mass or according to the system's defined characterization units) to provide rigid support and physical crosslinking points for the system. Simultaneously, the solution viscosity of the pressure-sensitive adhesive system is typically 25 (in units of viscosity measured under standard test conditions), thereby giving the system good flowability and coating adaptability during processing. This allows the pressure-sensitive adhesive to form a stable phase-separated structure at the microscopic level, where the PMMA hard segments form dispersed physical cross-linking domains, while the soft segments provide a continuous elastic phase. This achieves a balance between initial tack and holding power at the macroscopic level, ensuring that the dressing has good wetting and adhesion capabilities at the moment of application, while maintaining excellent cohesion and shear resistance during long-term use.
[0034] It should be noted that in step S1, the thermal dispersion treatment is performed by a heated disperser device, which provides the raw materials of the pressure-sensitive adhesive to the reaction vessel for stirring and mixing. This facilitates the full dispersion and uniform mixing of each component under controlled temperature and stable shear conditions, thereby improving the uniformity and stability of the raw material system. This lays the foundation for the formation of a stable continuous phase pressure-sensitive adhesive in subsequent steps, and ultimately enhances the adhesive performance of the final hydrocolloid dressing and the controllability of the preparation process.
[0035] In addition, this embodiment also provides the application of hydrocolloid dressings as medical dressings. Because hydrocolloid dressings contain hydrophilic components (such as sodium carboxymethyl cellulose, polyethylene glycol, etc.), they can absorb and lock in moisture upon contact with wound exudate or skin sweat, thereby reducing the accumulation of exudate on the skin around the wound or stoma, helping to maintain a suitable moist environment, reducing the risk of skin maceration, and improving skin protection. Furthermore, the hydrocolloid dressing has a soft and elastic structure, is composed of pressure-sensitive adhesive, and has good initial tack and sustained adhesion, allowing it to conform well to the curved structure of human skin. During application, it can adapt to deformation caused by human activity, improving wearing comfort and reducing the likelihood of dressing edges lifting or falling off.
[0036] Table 1 below lists the comparison data of each embodiment and the comparative example in terms of key performance indicators.
[0037] Table 1 Raw Material Composition Table Components Example 1 Example 2 Example 3 Comparative Example A (non-parental block) Comparative Example B (Low PIB 0.5) polymer colloids 24 24 24 24 24 PIB-H 32 32 32 32 0.5 GDP-L(Mw<1000) 10 10 10 10 0.5 Tackifying resin 3 3 3 3 3 glycerin 6 6 6 6 6 CMCNa 15 15 15 15 15 affinity block copolymer 10 10 8 0 10 ZnO 0.2 0.2 0.2 0.2 0.2 polyurethane 0.25 0.25 0.25 0.25 0.25 antioxidants 0.15 0.15 0.15 0.15 0.15 Table 2 below lists the performance test results.
[0038] Table 2 Performance Test Table index unit Example 1 Example 2 Example 3 Comparative Example A Comparative Example B Initial adhesion N / 25 mm 10.4 9.8 8.2 6.2 6.1 Shear hold h >72 >72 60 18 30 Peel retention rate after immersion in water % 86 88 82 45 55 Water absorption (24 h) % increase in quality 12.5 13.8 15.0 4.2 9.0 MTT (Mean Time Tolerance) % 96.5 95.8 97.2 92.1 94.0 Energy storage modulus E' (1 Hz) MPa 0.45 0.52 0.48 0.35 0.40 Peel strength decreases after aging % 6.2 4.8 8.5 28.4 18.9 Please see Figure 3 As can be seen from the table above, in Example 1 above, the initial adhesion was 10.4 N / 25 mm, shear retention was >72 h, peel retention rate after immersion in water was 86%, water absorption capacity was 12.5%, cell survival rate was 96.5%, and peel force decreased by 6.2% after aging.
[0039] In Example 2, based on Example 1, the molecular weight of PEG was increased (specifically from PEG-400 to PEG-2000), and the branching degree of polyglycerol decanoate was appropriately fine-tuned to optimize physical properties. Test results showed an initial tack of 9.8 N / 25 mm, shear retention >72 h, water retention rate of 88%, and a 4.8% decrease in peel strength after aging, which is significantly inferior to Example 1.
[0040] In Example 3, to enhance water absorption performance, while keeping the total amount of affinity block copolymer unchanged at 22 parts, the molecular weight of PEG was appropriately reduced and the dispersion uniformity treatment of sodium carboxymethyl cellulose was slightly increased. The water absorption capacity was measured to be 15.0%, but the aging stability remained within an acceptable range, and the peel strength decreased by 8.5%.
[0041] In Comparative Example A, without the presence of the affinity block copolymer, the formulation showed a significant decrease in water absorption capacity and water retention rate after immersion (water absorption 4.2%, water retention rate 45%), failing to meet the requirements for use in humid environments.
[0042] In Comparative Example B, significantly reducing the amount of high / low PIB (e.g., 0.5 parts each) resulted in a significant decrease in shear retention and long-term tackiness, with shear retention lasting only about 30 hours, thus highlighting the importance of the synergistic ratio of high / low PIB.
[0043] In other embodiments, for thermosensitive active ingredient-supported formulations, prolonged mixing at lower temperatures (105 to 110°C) and extended curing time at 60°C are performed to prevent loss of the thermosensitive components while maintaining good performance. Furthermore, after step S4, microencapsulated silver ions or anti-inflammatory drugs (0.1% to 1.0%) are introduced for anti-infection or healing promotion of the ostomy bag, resulting in drug release kinetics consistent with biocompatibility.
[0044] It should be noted that for the initial tack test: according to ASTM D3330 (180° peel, 300 mm / min), it is performed on a stainless steel substrate or artificial skin, and the average value is taken (n≥3).
[0045] For shear retention testing: Apply a 2 kg load to the metal plate according to PSTC-7 standard and record the failure time (in hours).
[0046] For the detection of peel retention rate after immersion in water: the sample was immersed in distilled water at 37℃ for 24 h, and then the peel force was measured according to the initial tack method. The retention rate (%) was obtained by comparing it with the unimmersed sample.
[0047] For water absorption testing: Take a 20×20 mm sample, dry and weigh it, then place it in an environment of 25℃ and 95% RH for 24 h, weigh it and calculate the percentage increase in mass.
[0048] For the detection of viscoelastic modulus: Dynamic mechanical analysis (DMA), frequency 1 Hz, record the storage modulus E' and loss modulus E''.
[0049] For aging tests: Store the samples at 40°C and 75% RH for 14 days, and then measure the performance changes.
[0050] The above are merely preferred embodiments of the present invention. The scope of protection of the present invention is not limited to the above embodiments. All technical solutions that fall within the scope of the present invention are within the scope of protection of the present invention.
Claims
1. A hydrocolloid dressing for an adhesive base plate of an ostomy bag, characterized in that, It is composed of pressure-sensitive adhesive; the raw materials of the pressure-sensitive adhesive include the following components in parts by weight: 24 parts of polymer colloid, 42 parts of polyisobutylene composition, 3 parts of tackifying resin, 6 parts of glycerol, 15 parts of sodium carboxymethyl cellulose, and 10 parts of affinity block copolymer; The polyisobutylene composition is high molecular weight polyisobutylene and low molecular weight polyisobutylene; The affinity block copolymer is polyethylene glycol and polyglycerol decanoate; The preparation method of this hydrocolloid dressing includes the following steps: S1: The polymer colloid, tackifying resin, and glycerin are sequentially added to the thermal dispersion treatment and heated and stirred. S2: While stirring, mix in the polyisobutylene composition formulated with high molecular weight polyisobutylene and low molecular weight polyisobutylene. After stirring and mixing evenly, a continuous phase pressure-sensitive adhesive is obtained. S3: Perform vacuuming, then cool down, and continue adding sodium carboxymethyl cellulose to the continuous phase pressure-sensitive adhesive while stirring; S4: Continuously heat and stir, and simultaneously mix polyethylene glycol and polyglycerol decanoate to prepare a pressure-sensitive adhesive; S5: Apply the pressure-sensitive adhesive to the adhesive base to obtain the hydrocolloid dressing.
2. The hydrocolloid dressing for ostomy bag adhesive baseplate according to claim 1, characterized in that, In step S2, the mixing temperature is 120°C to 125°C, the mixing time is 60 min to 65 min, and the stirring speed is 60 r / min to 65 r / min.
3. The hydrocolloid dressing for ostomy bag adhesive baseplate according to claim 2, characterized in that, In step S3, the temperature after cooling is 90°C to 100°C, and the stirring speed is 20 r / min to 30 r / min.
4. The hydrocolloid dressing for ostomy bag adhesive baseplate according to claim 2, characterized in that, In step S4, the mixing time is 80 to 90 minutes, and the mixing temperature and stirring speed are the same as in step S2.
5. The hydrocolloid dressing for ostomy bag adhesive baseplate according to claim 1, characterized in that, The high molecular weight polyisobutylene is 32 parts, and the low molecular weight polyisobutylene is 10 parts each, with the molecular weight of the low molecular weight polyisobutylene being less than 1000.
6. The hydrocolloid dressing for ostomy bag adhesive baseplate according to claim 1, characterized in that, The polyethylene glycol comprises 2 parts, and the polyglycerol decanoate comprises 8 parts; the polyethylene glycol is a hydrophilic material used to absorb interfacial moisture; the polyglycerol decanoate is a hydrophobic material used to provide viscoelasticity.
7. The hydrocolloid dressing for ostomy bag adhesive baseplate according to claim 1, characterized in that, The polymer colloid is a continuous phase colloid, and contains at least zinc oxide powder and polyurethane.
8. The hydrocolloid dressing for ostomy bag adhesive baseplate according to claim 1, characterized in that, The polymer colloid is an acrylate copolymer configured as a triblock structure consisting of styrene-isoprene-styrene.
9. The hydrocolloid dressing for ostomy bag adhesive baseplate according to claim 1, characterized in that, In step S1, the thermal dispersion process is performed by a heated disperser device for providing the raw materials of the pressure-sensitive adhesive to the reaction vessel for stirring and mixing.
10. The application of the hydrocolloid dressing according to claim 1 as a medical dressing.