海藻酸钙凝胶微球的制备和pH依赖性溶胀

利用海藻酸钠溶液与氯化钙溶液发生胶凝反应，本文用滴制的方法制备了海藻酸钙凝胶微球，并对制备的处方和工艺进行了探讨，同时考察了海藻酸钙凝胶微球的特征和溶胀特性。干燥的凝胶微球在不同pH的水性介质中溶胀特性不同。海藻酸钙凝胶微球的这种溶胀的pH敏感性，使其能成为口服药物缓释制剂的载体。     

硝苯地平海藻酸钙凝胶缓释微丸处方及工艺的优化

目的制备硝苯地平 海藻酸钙凝胶缓释微丸。方法采用滴制法。用单因素考察及均匀设计实验优化处方及工艺。结果优化得到的微丸在体外累计释放硝苯地平百分率 ,2h为 2 0 %～ 3 0 % ,6h为 60 %～ 80 % ,1 2h>85 %。结论在体外释放度实验中 ,硝苯地平海藻酸钙凝胶微丸具有良好的缓释作用     

海藻酸钙凝胶微球中模型药物的pH值依赖性释放

目的:考察海藻酸钙凝胶微球中模型药物的pH值依赖性释放.方法:以硝苯地平为模型药,采用滴制法制备了含药微球;考察了含药微球在不同pH值介质中的释放特性.结果:含药微球在水及pH 1.0的介质中几乎不溶胀,12 h累积释放百分率为23.1%和23.4%;在pH6.8的介质中微球溶胀至完全溶蚀,且呈现缓慢释放的趋势,12 h药物的累积释放百分率为92.5%;换介质的释放中,0～2 h微球几乎不溶胀,2 h累积释放8.4%,介质pH改变后微球很快崩解,3 h累积释放82.4%.结论:海藻酸钙凝胶微球中硝苯地平的释放具有pH值依赖性,在pH 6.8的介质中缓释.     

阿西美辛海藻酸钙凝胶微丸释药影响因素考察

目的:考察阿西美辛海藻酸钙凝胶微丸的释药机制。方法:采用滴制法制备阿西美辛海藻酸钙微丸,考察海藻酸钠浓度,钙离子浓度,投药量,滴头直径大小对药物释放的影响。结果:海藻酸钠浓度增加,钙离子浓度增加,滴头直径增加,释药速率减慢。结论:在体外释放度实验中,阿西美辛海藻酸钙凝胶微丸具有良好的缓释作用,海藻酸钙凝胶微丸是一种非常有潜力的药物载体。     

硝苯地平缓释凝胶的制备工艺及其释药性能研究

目的:制备硝苯地平缓释凝胶并考察其体外释药情况。方法:采用复凝聚法制备硝苯地平缓释凝胶,以壳聚糖、海藻酸钠的浓度、搅拌速度和壳聚糖溶液与海藻酸钠溶液的体积比为因素进行正交试验;用转篮法测定所制凝胶的释放度,通过改变释放介质的pH值,考察该缓释药物对pH的敏感性。结果:最佳工艺为壳聚糖浓度0.4%、海藻酸钠浓度1.5%、搅拌速度160r.min-1、壳聚糖溶液与海藻酸钠溶液的体积比为6:1。硝苯地平缓释凝胶在pH1.5的人工胃液中4h释放度为13.43%;在pH6.8的人工肠液中4h释放度为52.30%,12h释放度为81.72%。结论:所制硝苯地平缓释凝胶具有明显的缓释作用,体外释放具有较强的pH敏感性。     

卡维地洛pH敏感性N-琥珀酰壳聚糖-海藻酸钙水凝胶的制备工艺优选

目的:优选卡维地洛pH敏感性N-琥珀酰壳聚糖-海藻酸钙水凝胶的最佳制备工艺,并考察其pH敏感性。方法:以包封率和载药量为考察指标,采用L9(34)正交试验优选其制备工艺。评价水凝胶在不同pH值溶液中的pH敏感性。结果:优选的最佳工艺为2%(w/v)N-琥珀酰壳聚糖,2%(w/v)海藻酸钠,2%(w/v)氯化钙,药物与海藻酸钠的质量比为1∶4(g/g)。水凝胶在pH1.5的溶液中几乎不溶胀,在pH6.8的溶液中溶胀度最大。结论:优选的制备工艺合理可行,制备的水凝胶具有明显的pH敏感性及缓释效果。     

酮康唑海藻酸钙凝胶小球的制备工艺研究

目的:考察酮康唑海藻酸钙凝胶小球的制备工艺和最优处方。方法:采用滴制法制备海藻酸钙凝胶小球,以酮康唑的包封率和载药量作为制备工艺优化指标,设计正交试验优选最佳处方;测定最佳处方所制制剂的包封率(EE)和载药量(LD)并与原料药比较体外释放作用。结果:最优处方为海藻酸钠浓度2.0%,海藻酸钠与酮康唑质量比2∶1,氯化钙浓度0.3mol.L-1;EE和LD平均值分别为(90.53±2.32)%、(31.51±2.08)%,与原料药比较缓释性较好。结论:本法工艺简单、可行、稳定,重现性好。     

龟板水提物缓释微球的制备及其特性

目的：制备高包封率的龟板水提物缓释微球。方法：分别采用海藻酸钙凝胶珠、海藻酸钙-壳聚糖微胶囊和海藻酸钙-羧甲基纤维素钠微胶囊体系制备龟板水提物缓释微球,并考察其外观形态、包封率和体外释药等特性。结果：制得的龟板-海藻酸钙凝胶珠、龟板-海藻酸钙—壳聚糖微球和龟板-海藻酸钙-羧甲基纤维素钠微球外观圆整,表面光滑,且粒径均匀;包封率分别是46．7％、49．9％和82．3％;海藻酸钙凝胶珠有明显的突释现象,海藻酸钠—壳聚糖微球的突释现象和缓释效果有所改善,而海藻酸钙-羧甲基纤维素钠微球无突释现象,其缓释可达14小时以上。结论：龟板-海藻酸钙-羧甲基纤维素钠微球包封率高,同时具有优良的缓释性能。     

烟酸缓释微丸的制备及体外释放度考察

目的:制备24 h烟酸缓释微丸,考察其体外释放度。方法:使用离心造粒机,采用空白丸芯粉末上药法制备烟酸载药素丸;使用国产流化床包衣机,以乙基纤维素为包衣材料进行包衣。考察包衣处方因素、热处理条件和释放介质对释放度的影响。结果:烟酸素丸圆整度良好,光滑;16～20目收率约90%。包衣增重、致孔剂类型以及用量是影响药物释放的关键因素。烟酸缓释微丸在pH 1.2的盐酸溶液中释放较快,在水,pH 4.5的醋酸盐缓冲溶液,pH 6.8和pH 7.9的磷酸盐溶液中释放无明显区别。以乙基纤维素包衣增重9%,以PEG 4000为致孔剂用量37%,得到的缓释微丸具备体外24 h缓释特征。结论:该缓释微丸的体外释放符合缓释制剂要求。     

吲哚美辛结肠定位凝胶微丸的研究

目的制备吲哚美辛凝胶微丸实现结肠定位给药。方法采用滴制法制备海藻酸钙微丸,以微球圆整度、包封率、载药量为质量指标,通过正交试验选出优化处方,并用丙烯酸树脂Eudragit S100进行包衣。结果凝胶微丸在人工胃液和人工肠液中6 h累积释放率小于15%,而在人工结肠液中2 h达80%以上。结论所制得的吲哚美辛凝胶微丸符合结肠定位的基本要求。     

Adipic acid dihydrazide treated partially oxidized alginate beads for sustained oral delivery of flurbiprofen

In this study, periodate oxidation of sodium alginate was controlled such that the oxidized alginate could form isolatable beads with Ca⁺² ions. The beads of oxidized alginate having a degree of oxidation 1 mol%, entrapped 89% flurbiprofen and released almost all of its content within 1.5 h in pH 7.2 phosphate buffer solution. The beads were covalently crosslinked with adipic dihydrazide (ADH) in addition to ionic crosslinks and were characterized. Scanning electron microscopy revealed that the beads were spherical having smooth surfaces. The drug entrapment efficiency decreased (90–86%) with increasing concentration of ADH (2–6% w/v) in the gelation medium. However, the beads prolonged the drug release in alkaline dissolution medium up to 8 h depending upon the concentration of ADH. The beads prepared with 2% ADH swelled more rapidly and led to faster drug release in either pH 1.2 HCl solution or pH 7.2 phosphate buffer solution. The swelling tendencies were reduced and the drug release became slower with higher concentrations in either fluid. The drug diffusion from the beads followed super case II transport mechanism. FTIR spectroscopy indicated stable nature of flurbiprofen in the beads and therefore had potential as sustained oral delivery system for the drug.     

An anti-inflammatory drug (mefenamic acid) incorporated in biodegradable alginate beads: development and optimization of the process using factorial design

The objective of this study was to prepare and evaluate biodegradable alginate beads as a controlled-release system for a water-insoluble drug, mefenamic acid (MA), using 3 x 2(2) factorial design by ionotropic gelation method. Therefore, the mefenamic acid dispersion in a solution of alginate was dropped into the cross-linking CaCl(2) solution and a fairly high yield (71-89%) of MA-alginate beads were obtained. Their encapsulation efficiencies were in the range of 79.3-98.99%. The effect of drug:polymer ratio, CaCl(2) concentration, and curing time on the time for 50% of the drug to be released (t(50%)), and the drug entrapment efficiency were evaluated with factorial design method. It was found that drug:polymer ratio and interaction of drug:polymer ratio and curing time had an important effect on the drug to be released (t(50%)). The effect of CaCl(2) concentration is also important on the drug release. On the other hand, all factors except CaCl(2) concentration were effective on the drug entrapment efficiency. The swelling properties of beads were also studied. The release mechanism was described and found to be non-Fickian, Case II, and Super Case II transport for the formulations. This study suggested a new mefenamic acid alginate bead formulation for oral delivery of nonsteroidal anti-inflammatory drugs, which cause gastric irritation.     

Comparison of the pharmaceutical properties of sustained-release gel beads prepared by alginate having different molecular size with commercial sustained-release tablet

Spherical alginate gel beads containing pindolol were prepared using three types of sodium alginate with different molecular size. The rate of gelation of sodium alginate in calcium chloride solution was in the range of 1.0 to 1.3 h-1 among the used three alginates, but the amount of water squeezed from the alginate gel beads during gelation increased from 5 to 40% with increasing molecular size of the alginate. The beads prepared were similar in diameter (1.2 mm after drying), weight (0.9 mg/bead), calcium content (27-29 micrograms/bead) and pindolol content (40-45%). Pindolol was rapidly released from all the alginate gel beads at pH 1.2 owing to the high solubility of pindolol, in spite of non-swelling of beads. On the other hand, pindolol release from alginate gel beads at pH 6.8 was dependent on the swelling of the beads and was significantly depressed compared to drug powder. Interestingly, the release rate of pindolol and the swelling rate of beads were markedly slow for gel beads prepared by low molecular size alginate. However, when the alginate gel beads were administered orally to beagle dogs, the serum levels of pindolol showed sustained-release profiles, depending on the molecular size of the alginate. The in vivo absorption of pindolol from alginate gel beads did not reflect their in vitro release profiles, because of a physical strength of beads in the intestinal tract. Furthermore, the in vivo and in vitro release of pindolol from alginate gel beads were compared with a commercial sustained-release tablet, Carvisken showed a rapid release of 50% of content in pH 1.2 fluid and residual 50% of pindolol were easily dissolved at pH 6.8. Although the release characteristics of pindolol from Carvisken and the alginate gel beads were completely different, the serum levels of pindolol in human volunteers were comparable.     

The release behavior of brilliant blue from calcium-alginate gel beads coated by chitosan: the preparation method effect.

The aim of this study is to reveal how the release behavior of a model drug (brilliant blue, BB) from chitosan coating calcium-alginate gel beads (CCAGB) was influenced by the preparation methods. The CCAGB were prepared by dropping alginate solution into CaCl(2)/chitosan solution (method 1(a)), or into chitosan solution then gelled by CaCl(2) (method 1(b)), or into CaCl(2) solution then coated by chitosan (method 2). Scanning electron microscopy was used for morphology observation, and elemental analysis was applied to determine the chitosan content bound on calcium-alginate gel beads (CAGB). Compared to CAGB, the dried CCAGB had poorer shape and rougher surface morphology especially in methods 1(a) and (b); moreover, CCAGB was found to be more instable in 0.9% NaCl and serious burst of beads occurred when high concentration of alginate (3.0 and 5.0% w/v) was used. The influence on BB release from the beads by chitosan coating was not only related to the chitosan density on bead surface, but also preparation method and other factors. Under un-dried bead state in method 1(a), the increase of chitosan content prolonged BB release in 0.9% (w/v) NaCl; while in method 2, the increase of chitosan concentration over 0.1% (w/v) (3.0% (w/v) alginate concentration was used) resulted in more serious burst of beads and hence facilitated BB release. Furthermore, in both methods 1(a) and 2, the increase of alginate from 1.5 to 3.0 or 5.0% (w/v) usually resulted in the significant burst of beads and accelerated BB release when 0.3 or 0.5% (w/v) chitosan was used for coating. Drying process greatly influenced BB release profile due to the destroying of alginate-chitosan film. The acceleration of BB release from CCAGB by drying process was more significant in the case of method 1 than of method 2.     

Microencapsulation of a recombinant aminopeptidase (PepN) from Lactobacillus rhamnosus S93 in chitosan-coated alginate beads

A recombinant aminopeptidase (90 kDa) of Lactobacillus rhamnosus S93 produced by E. coli was encapsulated in alginate or chitosan-treated alginate beads prepared by an extrusion method. This study investigated the effects of alginate, CaCl2, chitosan concentrations, hardening time, pH and alginate/enzyme ratios on the encapsulation efficiency (EE) and the enzyme release (ER). Chitosan in the gelling solution significantly increased the EE from 30.2% (control) to 88.6% (coated). This polycationic polymer retarded the ER from beads during their dissolution in release buffer. An increase in alginate and chitosan concentrations led to greater EE and lesser ER from the beads. The greatest EE was observed in a pH 5.4 solution (chitosan-CaCl2) during bead formation. Increasing the CaCl2 concentration over 0.1 M neither affected the EE nor the ER. Increasing hardening time beyond 10 min led to a decrease in EE and the alginate:enzyme ratio (3 : 1) was optimal to prevent the ER.     

响应曲面法优化NSC/APT凝胶小球的制备工艺及其释药特性考察

目的 探索N-琥珀酰壳聚糖/凹凸棒黏土（NSC/APT）释药凝胶小球的制备工艺,考察其释药特性.方法 利用响应曲面法优化了制备工艺,采用安全无毒的氯化钙进行交联.结果 与结论通过响应曲面法优化的最佳工艺与模型拟合很好;所得凝胶小球的溶胀率和累积药物释放实验结果表明复合凝胶小球具有pH敏感性,在pH为1.2时基本不溶胀,3h药物仅释放0.66%;pH为5.8时溶胀率增加,3h药物累积释放达到62.55%;pH为6.8时溶胀率最大,药物释放速度最快,3h达到94.51%;但当pH增加至8.0时,溶胀率减小,3h释放了76.05%.琥珀酰壳聚糖的羧基在药物释放中起着关键作用.     

Controlling of systemic absorption of gliclazide through incorporation into alginate beads

This work investigates preparation of biodegradable beads with alginate polymer by ionotropic gelation method to take the advantages of the swelling and mucoadhesive properties of alginate beads for improving the oral delivery of the antidiabetic agent gliclazide. It demonstrates that the ionic gelation of alginate molecules offers a flexible and easily controllable process for manipulating the characteristics of the beads which are important in controlling the release rate and consequently the absorption of gliclazide from the gastrointestinal tract. Variations in polymer concentration, stirring speed, internal phase volume and the type of surfactant in the external phase were examined systemically for their effects on the particle size, incorporation efficiency and flow properties of the beads. The swelling behavior was strongly dependent on the polymer concentration in the formulations and the pH of the medium. The in vitro release experiments revealed that the swelling is the main parameter controlling the release rate of gliclazide from the beads. In vivo studies on diabetic rabbits showed that the hypoglycemic effect induced by the gliclazide loaded alginate beads was significantly greater and more prolonged than that induced by the marketed conventional gliclazide tablet (Gliclazide). The results clearly demonstrated the ability of the system to maintain tight blood glucose level and improved the patient compliance by enhancing, controlling and prolonging the systemic absorption of gliclazide.     

Alginate-diltiazem hydrochloride beads: optimization of formulation factors,in vitro and in vivo availability

Alginate beads containing diltiazem hydrochloride (DTZ) were prepared by the ionotropic gelation method. The effects of various factors (alginate concentration, additives type, calcium chloride concentration and curing time) on the efficiency of drug loading were investigated. The formulation containing a mixture of 0.8% methylcellulose (MC) and 4% alginate cured in 2% calcium chloride for 6 h was chosen as the best formula regarding the loading efficiency. The release rate of DTZ from various beads formulations was investigated. The release of drug from alginate beads followed two mechanisms; by diffusion and relaxation of the polymer at pH 1.2, whilst diffusion and erosion are at pH 6.8. The in vitro release of DTZ from MC-alginate beads showed an extended release pattern which was compared with that from commercially available sustained-release (Dilzem SR) and fast release tablets (Dilzem). Thermal analysis revealed that the drug was molecularly dispersed in the beads matrix. Although the release characteristics of DTZ from Dilzem SR and MC-alginate beads were completely different, the bioavailability of DTZ in dogs was comparable as measured by AUC, MRT and relative bioavailability. The absolute bioavailability of MC-alginate beads and Dilzem SR was 88 and 93%, respectively.     

Mechanisms of formation and disintegration of alginate beads obtained by prilling

In this paper, compendial sodium alginate beads have been manufactured by laminar jet break-up technology. The effect of polymer concentration, viscosity and polymeric solution flow rate on the characteristics of beads was studied. Size distribution of alginate beads in the hydrated state was strongly dependent on the flow rate and viscosity of polymer solutions, since a transition from laminar jet break-up conditions to vibration-assisted dripping was observed. The re-hydration kinetics of dried beads in simulated gastric fluid (SGF) showed that the maximum swelling of beads was reached after 1-2 h, with an increase in volume of two to three times and a time lag dependent on the polymer concentration. The re-hydration swelling profiles in simulated intestinal fluid (SIF) showed no time lag and higher swelling volume; moreover, in this medium after the maximum swelling was reached, the bead structure was quickly disaggregated because of the presence in the medium of phosphate able to capture calcium ions present in the alginate gel structure.     

Hydrocolloid carriers with filler inclusion for diltiazem hydrochloride release

Hydrocolloid beads based on agarose, alginate (both 3%, w/w), or gellan (2%, w/w) were produced to study their potential as drug carriers. The beads included various fillers: talc, kaolin, calcium carbonate, potato, or corn starch (10%, w/w). After gelation, the carriers were subjected to either freeze- or vacuum-drying. The dried carriers were spheroids. The diameters of freeze- and vacuum-dried carriers ranged from 2.4 to 4.1 mm and 1.5 to 2.8 mm, respectively. The porosity values of the freeze-dried carriers were significantly higher than those of their vacuum-dried counterparts. Scanning electron microscopy (SEM) revealed that all dried carriers included internal voids that were partially occupied by the filler particles. Upon their introduction into simulated gastric fluid (3 h), followed by 6 h in intestinal fluid, all carriers were stable and underwent swelling. Release profiles of diltiazem hydrochloride from different carriers were obtained during immersion in dissolution medium. Filler inclusion (but not the type of filler) contributed to the stability of the carriers and prolonged the time of drug release (6.5-8.5 h) relative to the faster drug release from carriers that contained no filler (3.5 h). In summary, alginate, agar, and gellan beads with filler inclusion may be useful for slow drug release.