泮托拉唑钠肠溶微丸胶囊的制备

以泮托拉唑钠、聚乙烯吡咯烷酮、滑石粉、磷酸钠、磷酸氢二钠和水混合制成主药层包衣溶液。采用流化床包衣技术,对空白丸芯依次包主药层、隔离层和肠溶层,制得泮托拉唑钠肠溶微丸,并优化了处方和工艺。将所得肠溶微丸装入普通胶囊中制成泮托拉唑钠肠溶微丸胶囊。3批制品在pH 6.8磷酸盐缓冲液中30 min时释放度分别为91.74%、87.98%、88.31%,在0.1 mol/L盐酸中2 h时的耐酸力分别为98.71%、97.18%、101.5%。     

兰索拉唑肠溶微丸胶囊的制备

目的:制备兰索拉唑肠溶微丸胶囊。方法:采用流化床包衣技术,在空白丸芯上依次包以主药层、隔离层和肠溶层,制备成兰索拉唑肠溶微丸,将肠溶微丸装入普通胶囊制成兰索拉唑肠溶微丸胶囊,并考察3批制剂的载药率及在人工肠液和人工胃液中的释放情况。结果:所制微丸圆整度高,外观亮泽,载药均匀、载药率高(平均值在96%以上),包衣效果好;其在人工肠液中45min的体外累积释放率大于(94.3±0.76)%,在人工胃液中2h的释放量小于(6.2±1.6)%。结论:所制兰索拉唑肠溶微丸胶囊工艺可行,重现性良好,质量稳定可靠,具有良好的体外释药性和耐酸力。     

娑罗子肠溶微丸胶囊的制备及质量评价

采用流化床底喷包衣法，对蔗糖丸芯依次包药物层、隔离层和肠溶衣层，制备娑罗子总皂苷提取物肠溶微丸。以微丸上药率、收率、工艺可行性、七叶总皂苷含量及2 h酸中释放量为评价指标，采用单因素试验结合多指标综合评价法优化肠溶微丸处方。照所得优化处方平行制备3批样品，并测得肠溶微丸的平均粒径为665.26μm，堆密度约为0.92 g/mL，脆碎度低于2.5%，总皂苷含量为(101.30±0.79)%。将所得肠溶微丸装入胶囊后进行体外释放度试验。结果显示，该肠溶微丸胶囊的2 h酸中释放量为(5.26±2.25)%，在磷酸盐缓冲液(pH 6.8)介质中45 min时基本释放完全。     

泮托拉唑钠肠溶微丸型片剂的制备

研究泮托拉唑钠肠溶微丸型片剂制备方法。采用流化床包衣法制备泮托拉唑钠肠溶微丸, 将肠溶微丸与适合的辅料混合采用直接压片法制备泮托拉唑钠微丸型片剂。用体外释放度法及扫描电镜法观察压片前后药物的体外累计释放量及微丸形态。结果表明, 优化处方: 衣膜增重55%, 增塑剂含量20%, Eudragit L30D-55/ NE30D为8∶2, 肠溶微丸/辅料 (MCC/PPVP/PEG 6000, 2∶1∶1) 为5∶5时, 肠溶片在0.1 mol·L⁻¹盐酸中2 h累积释放百分数<10%, pH 6.8磷酸盐缓冲液中1 h累积释放百分数>85%。制备的泮托拉唑钠肠溶微丸片的释药行为较好, 有望应用于工业生产。     

泮托拉唑钠肠溶微丸胶囊的处方工艺研究

目的研制泮托拉唑钠肠溶微丸胶囊。方法采用流化床包衣法制备泮托拉唑钠肠溶微丸,将制备好的微丸装入胶囊即得泮托拉唑钠肠溶微丸胶囊。结果胶囊在人工胃液中耐酸良好,在人工肠液中能够迅速溶出。结论该工艺简单易行、重现性良好、生产周期短、成本低、适合工业化生产。     

奥美拉唑肠溶微丸胶囊的制备及质量考察

目的制备奥美拉唑肠溶微丸胶囊。方法用离心制丸法直接制备载药母丸,再用流化床包衣法进行微丸包衣;采用正交试验设计对包衣液处方进行筛选优化,研究玉米朊在隔离层上的应用,采用新的肠溶层包衣处方。结果试验处方制得的奥美拉唑肠溶微丸稳定性好,酸性介质中2 h稳定性良好,耐酸力≥98%,p H 6.8缓冲液中释放达标,45 min体外释放度≥90%。结论采用药丸直接起母的方法简化了操作,降低了成本;选用玉米朊作为隔离层成膜材料,很好地提高了奥美拉唑的稳定性;在肠溶层中采用单硬脂酸甘油酯,既促进了微丸的体外释放,又增强了肠溶衣的稳定性。     

共载阿司匹林-埃索美拉唑镁肠溶微丸的研制与评价

在前期分别制备阿司匹林和埃索美拉唑镁肠溶微丸的基础上,本试验设计了共载阿司匹林-埃索美拉唑镁肠溶微丸。首先采用挤出-滚圆法制备含阿司匹林的丸芯,然后用流化床底喷包衣法,依次包隔离层Ⅰ、埃索美拉唑镁、隔离层Ⅱ和肠溶衣层,最终制得共载阿司匹林-埃索美拉唑镁的肠溶微丸。体外释放结果表明,该微丸中2种药物在0.1 mol/L盐酸中2 h内的累积释放率小于5%;随后在pH 6.8磷酸盐缓冲液中,15 min内阿司匹林和埃索美拉唑镁的累积释放率为(5.9±1.1)%和(78.5±1.4)%,60 min时为(77.4±3.3)%和(83.5±1.9)%。大鼠体内药动学结果表明,埃索美拉唑镁和阿司匹林的代谢产物水杨酸的tmax、AUC0→∞、cmax、MRT0→∞分别为(1.50±0.00)和(3.50±0.50)h、(15.73±2.50)和(1158.39±73.73)mg·L^-1·h、(2.89±0.09)和(75.13±2.14)mg/L、(8.30±1.30)和(11.68±0.60)h。本试验所得共载药微丸中埃索美拉唑镁在pH 6.8介质中能快速释药,阿司匹林则经一定时滞后再释放,有利于发挥两药协同作用,减轻阿司匹林长期应用对胃肠道的刺激性。     

兰索拉唑肠溶微丸的制备及处方优化

目的制备兰索拉唑肠溶微丸。方法采用流化床包衣技术,以空白丸芯为母核,依次包以主药层、隔离层、中性层和肠溶层,制备成兰索拉唑肠溶微丸,并对处方及工艺进行优化。结果按最佳处方工艺制备的3批兰索拉唑肠溶微丸释放度分别为96.4%、94.8%和94.3%。结论本方法制备的兰索拉唑肠溶微丸,工艺可行,质量可靠。     

重组水蛭素肠溶包衣微丸的制备及体外释放行为考察

目的研制重组水蛭素口服肠溶包衣微丸,并对其在不同pH释放介质中的释放行为进行考察,为重组水蛭素口服制剂的研究与开发提供实验依据。方法以羟丙甲基纤维素酞酸酯(HP55)为包衣材料,利用离心造粒机和流化床包衣设备制备重组水蛭素肠溶包衣微丸;采用二喹啉甲酸(BCA)法测定重组水蛭素肠溶包衣微丸的药物含量。结果所制备的重组水蛭素肠溶包衣微丸药物含量质量分数为3.513%。pH梯度释放实验结果表明,所研制的包衣微丸人工胃液中2 h药物仅释放4.98%;pH 5.8释放介质中继续释放,0.5 h释放82.13%,1 h释放95.47%;pH 7.2释放介质中继续释放,0.5 h释放97.53%,1 h释放98.33%。结论重组水蛭素肠溶包衣微丸在人工胃液中几乎不释药,可避免水蛭素被胃蛋白酶所降解;在人工肠液中药物释放快速而且完全,有利于水蛭素在肠道中的吸收。     

5-氨基水杨酸时控结肠定位控释微丸及其制剂的研制

目的制备5-氨基水杨酸微丸及其时控结肠定位控释释药系统的研究。方法首先采用挤出滚圆机制备了含药微丸,然后使用流化床包衣设备将微丸包衣,以羟丙甲纤维素和微粉硅胶的混合物包衣作为溶胀控释层,以乙基纤维素水分散体Surelease包衣作为时滞包衣层,并将包衣微丸装入肠溶胶囊。用释放度测定法研究微丸的释放行为。结果药物通过时滞层破裂开始释放,该层厚度增加可显著延长释药时滞。调节羟丙甲纤维素的型号、包衣增重及羟丙甲纤维素与微粉硅胶两者比例,可以控制药物释放速度。在模拟胃肠道pH情况下延迟5 h释药,之后的10 h内释药完全。结论可通过调整溶胀控释层包衣混合物的比例、型号、包衣厚度及时滞层的包衣厚度,制备5-氨基水杨酸时控结肠定位控释释药系统。     

SM-1小粒径肠溶微丸的制备及体外评价

目的制备SM-1小粒径肠溶微丸,并优化其处方,以达到肠溶和便于小动物给药的目的。方法采用流化床空白丸芯上药法,在丸芯表面依次包覆含药层、羟丙基甲纤维素（HPMC）隔离层和丙烯酸树脂（EudragitL30D-55）肠溶层。以载药量、耐酸性及释放度为指标,对SM-1肠溶微丸的处方进行优化。结果隔离层增重8%,肠溶层增重15%的肠溶微丸粒径〈450μm（40目筛）,圆整度良好,载药量约为20%;在pH为2.0的盐酸溶液中2 h内肠溶衣层薄层完好,药物释放度〈4%;在pH为6.8的PBS溶液中,45 min内释放度均〉70%。结论采用流化床制备SM-1肠溶微丸工艺可行,重现性好,具有良好的肠溶特性,粒径〈380μm,可用于小动物给药。     

阿莫西林脉冲释药微丸的研制

目的:制备阿莫西林脉冲释药微丸。方法:取空白丸芯分别以含药层、溶胀层(羧甲基淀粉钠)和控释层(乙基纤维素水分散体)顺序依次进行包衣制备阿莫西林脉冲释药微丸。采用紫外法和篮法考察溶胀层(12%、16%、20%)和控释层包衣增重(24%、28%、32%)及不同介质(水、盐酸、pH6.8磷酸盐缓冲液)对药物释放的影响。结果:溶胀层和控释层包衣增重对脉冲控释微丸的释药时滞和释放速率具有显著影响,药物释放情况不受介质pH值的影响;溶胀层和控释层包衣增重分别为16%、28%时制备的微丸时滞时间约为4h,时滞后4h累积释药率达到80%。结论:所制备的阿莫西林脉冲释药微丸具有体外脉冲释放作用。     

白术黄连微丸结肠靶向胶囊的制备及体外释放研究

目的 将中药"白术黄连方"制备成以胃溶微丸和肠溶微丸为基础的结肠靶向胶囊,优化其处方组成和制备工艺,考察其体外释放特性.方法 采用单因素实验和正交实验法优化微丸的处方组成和工艺参数.用挤出-滚圆技术制备素丸,流化床底喷方式进行包衣,考察隔离衣增重、肠溶衣中聚合物比例、增塑剂用量和包衣增重对肠溶微丸释放行为的影响,并对其...     

Development of a novel osmotically driven drug delivery system for weakly basic drugs

The drug substance SAG/ZK has a short biological half-life and because of its weakly basic nature a strong pH-dependent solubility was observed. The aim of this study was to develop a controlled release (cr) multiple unit pellet formulation for SAG/ZK with pH-independent drug release. Pellets with a drug load of 60% were prepared by extrusion/spheronization followed by cr-film coating with an extended release polyvinyl acetate/polyvinyl pyrrolidone dispersion (Kollidon SR 30 D). To overcome the problem of pH-dependent drug release the pellets were then coated with a second layer of an enteric methacrylic acid and ethyl acrylate copolymer (Kollicoat MAE 30 DP). To increase the drug release rates from the double layered cr-pellets different osmotically active ionic (sodium and potassium chloride) and nonionic (sucrose) additives were incorporated into the pellet core. Drug release studies were performed in media of different osmotic pressure to clarify the main release mechanism. Extended release coated pellets of SAG/ZK demonstrated pH-dependent drug release. Applying a second enteric coat on top of the extended release film coat failed in order to achieve pH-independent drug release. Already low enteric polymer levels on top of the extended release coated pellets decreased drug release rates at pH 1 drastically, thus resulting in a reversal of the pH-dependency (faster release at pH 6.8 than in 0.1N HCl). The addition of osmotically active ingredients (sodium and potassium chloride, and sucrose) increased the imbibing of aqueous fluids into the pellet cores thus providing a saturated drug solution inside the beads and increasing drug concentration gradients. In addition, for these pellets increased formation of pores and cracks in the polymer coating was observed. Hence drug release rates from double layered beads increased significantly. Therefore, pH-independent osmotically driven SAG/ZK release was achieved from pellets containing osmotically active ingredients and coated with an extended and enteric polymer. In contrast, with increasing osmotic pressure of the dissolution medium the in vitro drug release rates decreased significantly.     

Multiunit Controlled-Release Diclofenac Sodium Capsules Using Complex of Chitosan with Sodium Alginate or Pectin

This study explored the application of chitosan–alginate (CA) and chitosan–pectin (CP) complex films as drug release regulator for the preparation of multiunit controlled-release diclofenac sodium capsules. Pellets containing drug and microcrystalline cellulose, in a ratio of 3:5, were prepared in a fluidized rotary granulator. The pellets were coated with CA, CP, sodium alginate, pectin, and chitosan solutions. The pellets, equivalent to 75 mg drug, were filled into capsules. After 2 h of dissolution test in acidic medium, the amount of the drug released from any preparation was negligible. The pellets were further subject to pH 6.8 phosphate buffer. More than 80% drug release at 12 h was observed with the uncoated pellets and those coated with sodium alginate, pectin or chitosan. Both 1% CA and 3% CP coated pellets exhibited drug release profiles similar to that of Voltaren SR75. It was found that approximately 60% and 85% of the drug were released at 12 and 24 h, respectively. Both Differential thermal analysis (DTA) and Fourier transform infrared spectroscopy (FTIR) analyses revealed complex formation between chitosan and these anionic polymers. It could be concluded that CA and CP complex film could be easily applied to diclofenac sodium pellets to control the release of the drug.     

Multiunit controlled-release diclofenac sodium capsules using complex of chitosan with sodium alginate or pectin

This study explored the application of chitosan-alginate (CA) and chitosan-pectin (CP) complex films as drug release regulator for the preparation of multiunit controlled-release diclofenac sodium capsules. Pellets containing drug and microcrystalline cellulose, in a ratio of 3:5, were prepared in a fluidized rotary granulator. The pellets were coated with CA, CP, sodium alginate, pectin, and chitosan solutions. The pellets, equivalent to 75 mg drug, were filled into capsules. After 2 h of dissolution test in acidic medium, the amount of the drug released from any preparation was negligible. The pellets were further subject to pH 6.8 phosphate buffer More than 80% drug release at 12 h was observed with the uncoated pellets and those coated with sodium alginate, pectin or chitosan. Both 1% CA and 3% CP coated pellets exhibited drug release profiles similar to that of Voltaren SR75. It was found that approximately 60% and 85% of the drug were released at 12 and 24 h, respectively. Both Differential thermal analysis (DTA) and Fourier transform infrared spectroscopy (FTIR) analyses revealed complex formation between chitosan and these anionic polymers. It could be concluded that CA and CP complex film could be easily applied to diclofenac sodium pellets to control the release of the drug.     

多糖凝胶骨架结肠定位给药缓释系统的体外释放研究

目的: 筛选多糖材料作为水凝胶骨架,以达到结肠定位释药目的.方法: 选用海藻酸钠、果胶、壳聚糖、瓜木耳胶与药物混和制粒,灌装肠溶或结肠溶胶囊,考察其在人工胃液,人工肠液及人工结肠液中的释放情况.结果: 难溶性药物的海藻酸钠骨架结肠溶胶囊在人工胃液和小肠液中均不释放,人工结肠液中3 h释药低于30%;果胶骨架肠溶胶囊在人工胃液亦不释药,人工肠液中5 h释药仅为15%.水溶性药物在人工肠液中5 h释放可达50%.结论: 难溶性药物的海藻酸钠/结肠溶胶囊和果胶/肠溶胶囊体外释放度结果符合结肠定位的要求,可以作为建立酶触发体外释放评价方法和体内评价的制剂形式.水溶性药物的果胶/肠溶胶囊是较理想的缓释剂型.     

盐酸罗沙替丁醋酸酯脉冲控释微丸的研制

目的:制备盐酸罗沙替丁脉冲控释微丸(ROXPCP)。方法:取空白丸芯分别以含药层、溶胀层(含交联羧甲基纤维素钠)和控释层(含乙基纤维素水分散体)顺序包衣制备ROXPCP,通过考察不同类型空白丸芯、溶胀层材料及溶胀层与控释层的不同包衣增重对药物释放的影响来优选工艺,并进行处方验证试验。结果:各考察因素均对药物的释放影响显著。优选工艺结果为:空白丸芯采用蔗糖型,溶胀层材料采用交联羧甲基纤维素钠,溶胀层和控释层包衣增重分别为15%、24%。以此制备的微丸时滞时间为4h左右,时滞后4h内累积释药百分率达到80%。结论:所制备的ROXPCP具有体外脉冲控释作用。