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The hydrophobic monomer, n-butyl methacrylate (BMA) has been incorporated into thermoresponsive poly(N-isopropylacrylamide) (PIPAAm) to lower PIPAAm phase transition temperatures necessary for systematically regulating cell adhesion on and detachment from culture dishes at controlled temperatures. Poly(IPAAm-co-BMA)-grafted dishes were prepared by electron beam irradiation methods, systematically changing BMA content in the feed. Copolymer-grafted surfaces decreased grafted polymer transition temperatures with increasing BMA content as shown by water wettabilities compared to homopolymer PIPAAm-grafted surfaces. Bovine endothelial cells readily adhered and proliferated on copolymer-grafted surfaces above collapse temperature at 37°C, finally reaching confluence. Cell sheet detachment behavior from copolymer-grafted surfaces depended on the culture temperature and BMA content. In conclusion, cell attachment/detachment can be controlled to an arbitrary temperature by varying the content of hydrophobic monomer incorporated into PIPAAm grafted to culture surfaces. © 2004 Wiley Periodicals, Inc. J Biomed Mater Res 69A: 70–78, 2004

Fabrication of functional tissue constructs using sandwiched layers of cultured cells could prove to be an attractive approach to tissue engineering. Rapid detachment of cultured cell sheets is a very important recovery method that permits facile manipulation of the sheet and prevents functional damage. To accelerate the required culture substrate hydrophilic and hydrophobic structural changes in response to culture temperature alteration, poly(N-isopropylacrylamide) (PIPAAm) was grafted onto porous culture membranes by electron beam irradiation. Analyses by attenuated total reflection-Fourier transform IR and electron spectroscopy for chemical analysis revealed that PIPAAm was successfully grafted to surfaces of porous membranes. Atomic force microscopy (AFM) results showed that PIPAAm-grafted membranes had smoother surfaces than ungrafted controls while retaining their porous structure. The mean roughness of PIPAAm-grafted and -ungrafted porous membrane surfaces determined by digital AFM autocalculation was 4.40 +/- 0.4 and 5.9 +/- 0.4 nm, respectively. Tissue culture polystyrene (TCPS) dishes grafted with PIPAAm were compared with PIPAAm-grafted porous membranes in cell sheet detachment experiments. Approximately 75 min was required to completely detach cell sheets from PIPAAm-grafted TCPS surfaces compared to only 30 min to detach cell sheets from PIPAAm-grafted porous membranes. With porous membranes, the water accesses the PIPAAm-grafted surface from underneath and peripheral to the attached cell sheet, resulting in rapid hydration of grafted PIPAAm molecules and detachment of the cell sheet. With TCPS PIPAAm-grafted surfaces the water is supplied from only the periphery of a cell sheet, slowing detachment.

To investigate the influence of molecular architecture of poly(acrylic acid) (PAAc)-graft-poly(N,N-dimethylacrylamide) (PDMAAm) (PAAc-g-PDMAAm) on its solution properties in aqueous media, graft copolymers were synthesized by free radical copolymerization of AAc with PDMAAm macromonomer. PAAc-g-PDMAAms were water-soluble at lower temperatures, while they showed a liquid−liquid phase separation from water above the characteristic transition temperatures. The phase transition behavior was affected by the copolymer compositions and pH of the solution. Below the transition temperature, hydrogen-bonding formation between AAc and DMAAm units was observed in the PAAc-g-PDMAAm aqueous solution by FT-IR−ATR measurement. Graft copolymers were thus formed spherical associates with a diameter of ca. 150 nm estimated from the dynamic light scattering measurement. At higher temperatures, the dehydrated regions and the weak dehydration of the PDMAAm chains induced cooperatively the hydrophobic aggregation, resulting in ...

To fabricate peptide delivery systems using polymeric drug carriers, an oligopeptide model drug, [Arg8]-vasopressin(AVP), was incorporated into nano-associates comprising poly(ethylene glycol)-( l -aspartic acid block copolymer (PEG-P(Asp)). Incorporation of the AVP was accomplished using a dialysis method. Static light scattering measurements revealed that the acid-type and mixture-type PEG-P(Asp)s formed nano-associates independently without AVP, while the salt form PEG-P(Asp) did not. High loading of AVP into acid-type PEG-P(Asp) was observed with loading levels controlled by changing the molar ratio of drug and block copolymer. Mixture-type PEG-P(Asp) did not show high loading and the salt-type PEG-P(Asp) form did not at all. Acid-type P(Asp) homopolymer formed associates including AVP, however, it was insoluble in aqueous medium. Dynamic light scattering measurements showed that the acid-type PEG-P(Asp) associates sizes narrowly clustered around 150 nm. This finding suggests that associates of acid-type PEG-P(Asp) effectively incorporates peptides possibly via a hydrogen bonding interaction between the block copolymer and the peptide.

Poly(6-(acryloyloxymethyl)uracil) (PAU) having uracil moieties as side chains was synthesized by ordinary radical polymerization to investigate its molecular discrimination for soluble nucleic acid bases in terms of phase transition changes of the polymer aqueous solution. PAU itself in distilled water formed a precipitate due to the polymer complexes at lower temperatures and changed drastically to become water-soluble above a characteristic transition temperature, showing an upper critical solution temperature (UCST). The phase transition behavior was shifted to lower temperatures with increasing concentrations of adenosine (Ado), which is the complementary nucleic acid base to uracil moiety. Ado might interact specifically with uracil moieties of the polymers, preventing the formation of the polymer complex at lower temperatures. Such changes were not observed in PAU aqueous solution containing guanosine (Guo). Additions of Ado and Guo exerted different effects to phase transition changes of the polymer. Moreover, addition of poly(adenylic acid) (Poly(A)) lowered remarkably the transition behavior of PAU solution as compared with Ado addition. It was conceivable that PAU and Poly(A) formed stable polymer complexes, assuming soluble states in even cold water. PAU changed its phase-transition temperature in response to species of the additive materials, demonstrating the specific molecular discrimination in aqueous milieu.

To achieve a combination of spatial specificity in a passive manner with a stimuli-responsive targeting mechanism, a temperature-responsive polymeric micelle is prepared using block copolymers of (poly(N-isopropylacrylamide-b-butylmethacrylate) (PIPAAm-PBMA)). The micelle inner core formed by self-aggregates of PBMA segments successfully loaded with a drug (adriamycin), and the outer shell of PIPAAm chains played a role of stabilization and initiation of micellar thermo-response. Optimum conditions were investigated for the micelle formation and drug loading into the inner cores in a view of micellar stability and function as drug carriers. Outer shell hydrophilicity that prevents inner core interaction with biocomponents and other micelles can be suddenly switched to hydrophobic at a specific site by local temperature increase beyond the LCST (lower critical solution temperature) (32.5 degrees C). These micelles showed reversible structural changes allowing drug release upon heating/cooling thermal fluctuations through the LCST. Polymeric micelles incorporated with adriamycin showed a dramatic thermo-responsive on/off switching behavior for both drug release and in vitro cytotoxicity according to the temperature responsive structural changes of a micellar shell structure. The reversible and sensitive thermo-response of the micelle opens up opportunities to construct a novel drug delivery system in conjunction with localized hyperthermia.

WWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWWW Poly(ethylene glycol-b-lactide) possessing a methoxygroup at the poly(ethylene glycol) (PEG) chain end anda polymerizable methacryloyl group at the poly(lacticacid) (PLA) chain end (MeO–PEG/PLA–methacryloyl)was prepared by an anionic ring-opening polymerizationof ethylene oxide and DL -lactide in tandem mannerinitiatedwithapotassium2-methoxyethanolate,followedby end-capping with an excess of methacrylic anhydride.The molecular weight of the obtained polymer wascontrolled by the initial monomer/initiator ratio, whichwas confirmed by the combination of gel permeationchromatography and nuclear magnetic resonance ana-lyses. The functionality of the methacryloyl–PLA endwas almost quantitative. The MeO–PEG/PLA–metha-cryloyl (38/35; these numbers in parentheses denote themolecular weights of PEG and PLA segments divided by100, respectively) formed a core–shell type sphericalmicelle in aqueous media obtained by a dialysistechnique, the cumulant diameter of which was ca.30nm with very low polydispersity factor.The methacryloyl group adjacent to the PLA waspolymerized in the PLA core of the micelle. Thepolymerizationproceededthermallywithradicalinitiatorand photochemically with photo-initiator to producecore-polymerized nanoparticles, which was found byspectroscopic and light-scattering techniques. Taxol-incorporated micelles were prepared to entrap Taxol intoMeO–PEG/PLA–methyacryloyl block copolymer mi-celles by the oil/water emulsion method. Copyright O1999 John Wiley & Sons, Ltd.KEYWORDS: polymeric micelle; stable nanoparticle;drugdeliverysystem;PEG/PLAblockcopolymer;micellestability; taxol

Adriamycin (ADR)-loaded thermally responsive polymeric micelles composed of poly( N -isopropylacrylamide- co - N , N -dimethylacrylamide)- b -poly( d,l -lactide) were prepared by dialysis from its dimethylacetamide solution against water. Microfiltration was successfully applied to removal of block copolymer associates, which were smaller than micellar structures. By this microfiltration polymeric micelles showing a lower critical solution temperature (LCST) at 40°C in phosphate buffered saline was obtained with a monodispersed size distribution of 69.2 nm in cumulant average diameter. ADR-loaded micelles released more ADR at 42.5°C (above the LCST) than at 37°C (below the LCST). ADR-loaded micelles did not show much cytotoxic activity against bovine aorta endothelial cells at 37°C, in contrast to high cytotoxicity at 42.5°C. On the other hand, free ADR expressed high cytotoxicity at both the incubation temperatures. Thus, thermally responsive polymeric micelles showed distinct control of ADR cytotoxic activity by temperature, while free ADR did not. From these results, an effective target therapy against solid tumors is feasible for these polymeric micelles by a combination of selective delivery to tumor sites based on stable micellar structures at 37°C and enhanced cytotoxic activity of these drug-loaded micelles at 42.5°C by local heating at tumor sites.

Four types of hydrophilic gel microcapsules containing water have been prepared by an interfacial polymerization method. Each type of microcapsules has a membrane of different composition. Using three kinds of monomers, N,N-dimethylacrylamide (DMAAm), 4-(aminomethyl)styrene (AmSt), and N,N-dimethylaminopropylacrylamide (DMAPAA), one type of aqueous copolymer having primary and tertiary amino groups was obtained. By the polymerization of three kinds of monomers, DMAAm, AmSt, and 2-[(methacryloyloxy)ethyl] trimethylammoniumchloride (METAC), another type of aqueous copolymer having primary and quaternary ammonium groups was also obtained. Two more types of copolymers were synthesized by copolymerization of α-acryloxy-ω-methoxy-poly(ethylene glycol) (a-PEG) with the above two kinds of monomer mixture. These copolymers were polymerized with terephthaloyldichloride at the water/oil interface to prepare four types of microcapsules containing water, i.e., poly(DMAAm-co-DMAPAA-co-AmSt-alt-terephthalic acid) microcapsules, poly(DMAAm-co-DMAPAA-co-AmSt-co-PEG-alt-terephthalic acid) microcapsules, poly (DMAAm-co-METAC-co-AmSt-alt-terephthalic acid) microcapsules, and poly (DMAAm-co-METAC-co-AmSt-co-PEG-alt-terephthalic acid) microcapsules, which will be abbreviated to MC 1, MC 2, MC 3, and MC 4, respectively. It has been predicted that the microcapsule membranes are hydrophilic and soft and have two-sublayer structures from electrophoretic mobility measurements and from the analysis of the data with Ohshima’s electrokinetic theory for soft particles. The outer sublayers of MC 1 and MC 2 are negatively charged and those of MC 3 and 4 are slightly positively charged. Also, the surfaces of MC 1 and MC 2 are harder than those of MC 3 and 4. By PEGylation, the surface charge density in the membranes decreases and the surface becomes softer. It has been found that the membrane of red blood cells (RBC) is also soft and is composed of two-sublayers, the outer sublayer of which is negatively charged and the inner one is positively charged. The interaction of four types of microcapsules with RBC has been studied. It was found that microcapsules with soft surfaces (MC 3 and MC 4) do not interact with RBC, even though the microcapsule surfaces are positively charged and the surface of RBC is negatively charged. On the other hand, microcapsules with negatively charged but harder surfaces (MC 1) interact with RBC to introduce hemolysis. The membrane surface of MC 2, which is obtained by PEGylation of MC 1, becomes softer than that of MC 1 so that the interaction with RBC was weakly suppressed. From these, it was concluded that the dominant factor to control the interaction between synthetic polymer surfaces and biological cell surfaces is not the surface charges carried by the polymer surfaces but the softness of the polymer surfaces.

Cross-linked poly(N-isopropylacrylamide) (PIPAAm) hydrogel-modified surfaces were prepared to investigate the effects of a three-dimensionally cross-linked structure of PIPAAm layers on both wettability changes and hydrophobic interactions with hydrophobic solutes in response to temperature changes. The temperature-responsive surface was prepared by polymerization of IPAAm in the presence of cross-linker on the substrates on which an azo polymerization initiator was covalently bonded. The PIPAAm hydrogel-modified surface showed temperature-responsive hydrophilic/hydrophobic surface property alterations as demonstrated by a large and discontinuous wettability changes in a range of 27−32 °C, a slightly lower temperature range than the phase transition temperature for soluble PIPAAm in aqueous media. This implies that the dynamic motion in response to temperature for PIPAAm segments in the modified hydrogel is restricted due to the cross-linked structure. The effect of the three-dimensional PIPAAm structure ...

Two types of thermo-responsive hydrogels are synthesized to obtain comb-type grafted gels with different lower critical solution temperatures (LCSTs) between graft chains and cross-linked backbone networks: these are poly(N-isopropylacrylamide) (PIPAAm) cross-linked hydrogels grafted with poly(N-isopropylacryl amide-co-N,N-dimethylacrylamide) (poly(IPAAm-co-DMAAm)) maintaining a freely mobile end and poly(IPAAm-co-DMAAm) cross-linked hydrogels grafted with PIPAAm chains. The effect of graft chain hydrophilic/hydrophobic balance as well as its mobility on deswelling kinetics of these grafted gels are investigated through the polymer LCST modulation and external temperature changes. The deswelling rate of poly(IPAAm-co-DMAAm)-grafted PIPAAm gel increases with increasing in temperature. This gel shows a discontinuous increase of the deswelling rate when the temperature is applied from below to above the graft chain LCST (37 degrees C). The deswelling rate of PIPAAm-grafted poly(IPAAm-co-DMAAm) gel increases continuously when the temperature is applied from below to above the graft chain LCST (31 degrees C). Due to the strong hydrophilicity of backbone network, the hydrophobic aggregation force weak. In contrast to the graft-type gels, normal-type poly(IPAAm-co-DMAAm) cross-linked gel without graft chains demonstrates the discontinuous decrease for the deswelling rate when the temperature is applied from below to above the polymer LCST (36 degrees C), entrapping water inside the gel due to the formation of an impermeable dense skin layer at the gel surface. These gel deswelling mechanisms are discussed in terms of gel structures.

Purpose. To determine aortic endothelial cells permeation ability and mechanisms of the aqueous block copolymeric micelles, poly(ethylene oxide)-poly ((β-benzyl L-aspartate) (PEO-PBLA) chemically conjugated with fluroescein isothiocyanate (FITC) by transport study and confocal laser scanning microscopy.

Block copolymer micelles (polymer−metal complex micelles) containing platinum(II) complexes in the core were prepared through the complexation of cis-dichlorodiammineplatinum(II) (cisplatin, CDDP) with poly(ethylene glycol)−poly(α,β-aspartic acid) block copolymer (PEG−P(Asp)) in an aqueous medium. Dynamic light scattering measurements revealed that CDDP-complexed micelles had diameters of approximately 20 nm with considerably narrow distribution. The critical substitution molar ratio of CDDP to Asp residues in PEG−P(Asp) (CDDP/Asp) to form a stable micelle structure was determined to be 0.5. The CDDP-complexed micelle, which was stable in distilled water at room temperature, started to dissociate in approximately 10 h of the induction period accompanying the sustained release of platinum(II) complex from the micelle in physiological saline (0.15 M NaCl solution) at 37 °C. The release rate of CDDP was inversely correlated with the chain length of P(Asp) segments in the block copolymer. This property of sus...

Four types of hydrophilic gel microcapsules containing water have been prepared by an interfacial polymerization method. Each type of microcapsules has membranes of different compositions. By the combination of three kinds of monomers, N , N -dimethylacrylamide (DMAAm), 4-(aminomethyl)styrene (AmSt), and N , N -dimethylamino-propylacrylamide (DMAPAA), two types of water-soluble copolymers having tertiary amino groups were obtained. Two more types of copolymers were synthesized by copolymerization of above three monomers with α -acryloxy- ω -methoxy-poly(ethylene glycol) (a-PEG). These four types of copolymers were polymerized with terephthaloy-dichloride at the water/oil interface to prepare four types of microcapsules containing water. Effects of the stirring rate during the preparation of microcapsules upon the membrane properties were studied. The effects of relative permittivity of dispersing media on microcapsule sizes were studied. It was found that the microcapsule sizes are controlled by the composition of the membranes and by the relative permittivity of the solvents in which microcapsules are redispersed. Depending on the stirring rates during the preparation procedure, the different changes in microcapsule size were observed during the exchanges of dispersing media of various relative permittivities. From these results, it is concluded that different microcapsules in their membrane compositions and in their properties are obtained depending on the stirring rate during the preparation of microcapsules, even if other preparation conditions are kept constant.

Deswelling mechanism for comb-type grafted poly( N -isopropylacrylamide) (PIPAAm) hydrogel was investigated to make clear the effect of gel architecture on the gel deswelling kinetics. Deswelling rate and mechanism were compared with those for conventional crosslinked PIPAAm gel and poly(ethylene oxide) (PEO)-grafted PIPAAm gel in response to temperature increase from below to above the gel-phase transition temperatures. The deswelling rate for the conventional PIPAAm gel are reciprocal to the gel size square, indicative of collective diffusion mediated manner for crosslinked network into water. Although PEO graft chains formed water release channels within the network to produce fast gel deswelling changes, deswelling change of PEO-grafted gel also demonstrated collective diffusion mediated manner of crosslinked backbone chains. On the other hand, one order faster rate of deswelling change of PIPAAm-grafted gel was observed than that of PEO-grafted gel with identical gel dimension. The deswelling change of PIPAAm grafted gel did not obey collective diffusion mediated manner, demonstrating reciprocal to the gel size to 1.58th power. This deswelling mechanism was explained in terms of rapid hydrophobic aggregation of freely mobile PIPAAm graft chains and an operation of intrinsic elastic forces of polymer network. The operation of both elastic force and strong hydrophobic aggregation force between the dehydrated PIPAAm graft chains released water inside the gel, causing more rapid deswelling changes of the PIPAAm-grafted gels.

Poly(ethylene oxide) (PEO) chains are introduced as graft chains maintaining freely mobile ends in thermo-responsive cross-linked poly(N-isopropylacrylamide) (PIPAAm) hydrogels by copolymerization of IPAAm with α-acryloyl-ω-methoxy-PEO. The deswelling response on raising the temperature of this gel above the gel phase transition temperature (TP) takes place within 10 min, whereas a conventionally cross-linked PIPAAm gel of the same dimensions requires 1 month for deswelling. This difference is due to the formation of water release channels within the skin layer by the hydrophilic PEO graft chains. The rapid deswelling of the grafted gel is compared with the deswelling changes of random copolymer gels composed of IPAAm and hydrophilic acrylic acid (AAc), which also accelerates gel deswelling. Deswelling is fastest in copolymers containing 1.3 wt % AAc and in grafted gels containing 13 wt % PEO. These results were interpreted as reflecting the gel structure.

A novel UV crosslinkable co-polymer of 4-(N-cinnamoylcarbamide)methylstyrene (CCMS) and N-isopropylacrylamide (IPAAm) was partially entrapped in traditional tissue-culture-treated polystyrene and crosslinked by UV light irradiation. Dishes modified by this method showed a change in contact angle with respect to temperature as compared to tissue culture polystyrene controls. Surface chemical analysis indicated that the crosslinked hydrogel does not detach from the surface after successive rinsing in ethanol and water, keeping the cells or cell construct free of unwanted soluble polymer after detachment. Cultures of both bovine endothelium and human retinal pigmented epithelium were confirmed to be able to attach and grow on the polymer-modified surfaces morphologically identical to that on control tissue culture polystyrene surfaces. Corresponding to a change in temperature, these cultures would detach and could be transplanted to another culture surface without functional and structural changes. These results show that the new, photo-crosslinkable hydrogel system can utilize the hydrophobic/hydrophilic change of the surface for cell culture detachment while being permanently applicable to any tissue culture geometry. © 1998 John Wiley & Sons, Inc. J Biomed Mater Res, 40, 631–639, 1998.

本研究では, グラフト鎖を有する分子構築ゲルにより, 温度変化に応答して素早く膨潤・収縮変化するゲルを実現し, 三次元網目鎖の凝集による水の押し出しと同期させて薬物をパルス的に放出する, 薬物放出制御の実現を目的として研究を行った.温度応答性ポリN-イソプロピルアクリルアミドの三次元網目中に, ポリエチレングリコールをグラフトしたゲルを合成した.ゲルは昇温変化で膨潤状態から収縮状態へと変化するとき, グラフ鎖が水のチャンネルを形成することにより, 主鎖の網目の凝集変化にともなうゲル内の水を素早くゲルの外へ押し出す透過チャンネルの役目を果たし, ゲルは素早く収縮変化した.これは, 三次元網目構造のポリN-イソプロピルアクリルアミドゲルが収縮変化するとき, 表面に緻密な高分子鎖からなるスキン層を形成し, 水の透過を抑制するため, ゲルの収縮変化がゆっくりとなるのときわめて対照的であった.さらに, ゲルの収縮変化にともなう薬物放出挙動が, 従来のゲルとグラフト型ゲルで大きく異なることが明らかにされた.すなわち, 従来のゲルが透過性の低いスキン層を形成し薬物拡散を抑制するのに対し, グラフト型ゲルは収縮変化による水の押し出しと同期させて, 内包した薬物を一気に押し出して放出し, パルス型の薬物放出挙動を示した.このグラフト鎖を有する分子構築ゲルによる, 温度応答性の薬物放出制御の特性を薬物の分子量を変化させて検討した.水の押し出し挙動と放出される薬物の分子量との相関を, 従来型のPIPAAmゲルの場合と比較しながら詳細に議論した.

Novel hydrophilic-hydrophobic block copolymers - poly(2-hydroxyethyl methacrylate-block-4-bis(trimethylsilyl)methylstyrene) (poly(HEMA-block-BSMS) or BH polymer) - were prepared as materials potentially useful for blood-contacting devices. Among the BH(X) series including poly(HEMA) itself, platelet adhesion and activation are minimum on the surface of BH(10), the block copolymer composed of 10 mol% of the hydrophobic segment. The unique physicochemical characteristics of BH(10) such as the high free water content and the increased mobility of PHEMA segments seem to play an important role in the prevention of platelet adhesion and activation. The water content of BH(10) was twice that of poly(HEMA) itself, even in the presence of 10 mol% of the hydrophobic moiety [poly(BSMS)]. Further, an anomalous increase in free water content was observed for the BH(10) sample measured by DSC. The glass transition temperature of BH(10) in the dry state was determined to be c. 10 degrees C, which was much lower than that observed for each of the homopolymers (c.f.: Tg [poly(HEMA)] = 70 degrees C; Tg [poly(BSMS)] = 160 degrees C), suggesting an increased mobility of tethered PHEMA segments in the BH(10) film.

Purpose. To directly visualize and evaluate the aqueous block copolymeric micelles, poly(ethylene oxide)-poly(β-benzyl L-aspartate) (PEO-PBLA) chemically conjugated with pyrene fluorescence molecule, by nanotechnology of atomic force microscopy (AFM).

Copolymers (IABb) composed of N-isopropylacrylamide (I), N-(3-dimethylaminopropyl)-acrylamide (A), 3-acrylamidophenylboronic acid (B), and a hydrophobic comonomer, n-butyl methacrylate (b), were synthesized as cell culture substrata since we previously learned that bovine aortic endothelial cells (BAECs) cultured on the phenylboronic acid-containing copolymer (IAB) differentiated into capillary structures after 26 days culture. The synthesized IABb copo ymers contained higher boron and amine moieties than the IAB copolymer. The results of the dynamic contact angle measurement revealed that IABb copolymer-coated surfaces showed a relatively hydrophobic nature, changing to hydrophilic in response to the aqueous environment. BAECs cultured on the copolymer substrata developed into capillary networks after 7 days. This is probably due to the enrichment of boron and amine segments in the vicinity of the hydrophilic copolymer surface, enhancing more pronounced interaction of boronates with cell membrane glycocalyx. The introduction of n-butyl methacrylate into the polymers might enhance the diffusion of the hydrophobic segments to the bulk polymers and the concentration of relatively hydrophilic segments at the outermost polymer surfaces by contact with water. A copolymer (IAP) without boronic acid groups was also prepared using N-phenylacrylamide (P) as a comonomer instead of 3-acrylamidophenylboronic acid in the IAB copolymer to investigate the effect of boronic acid moieties on the capillary formation of the cultured cells. Although the endothelial cells seeded on the copolymer without boronic acid groups adhered during the early culture period, these cells showed neither proliferation nor differentiation and detached from the surface after 13 days. These results strongly support the opinion that the phenylboronic acid groups in the copolymers are responsible for the specific induction of tissue formation of BAECs through the interaction with glycoconjugates on the cell membranes.

Alkyl-terminated PIPAAm was obtained by covalent coupling of alkyl groups of different chain lenghts (C3, C6, C8, C12 and C18) to one end of poly(N-isopropylacrylamide) (PIPAAm). At the molecular level, incorporation of the alkyl chains with PIPAAm chains promoted aggregation at temperatures below the LCST (lower critical solution temperature) of pure PIPAAm, reflecting the hydrophobic contribution of the alkyl chains to the LCST. The LCST changes were greatest for stearoyl (C18)-terminated PIPAAm (PIPAAm-C18H35). Interestingly, this polymer above its critical micelle concentration (cmc, 80 mg/L) in aqueous solution had the same LCST as unmodified PIPAAm, owing to formation of a core-shell micellar structure shielding the hydrophobic inner alkyl core from interactions with water. Micelle formation and the micellar structure of the alkyl-terminated PIPAAm aqueous dispersions were analyzed by fluorescence, surface tension and DLS (dynamic light scattering) measurements. Micelle formation is facilitated by both an increase in hydrophobicity of the incorporated group and suppression of PIPAAm hydrophilicity upon heating, closely relating to intramolecular hydrophilic/hydrophobic balance. PIPAAm-C18H35 micelles exhibit two heterogeneous microdomains; a hydrophobic inner core highly capable of solubilizing hydrophobic pyrene molecules, plus a hydrated outer shell that stabilizes this micellar structure below its LCST and shows reversible thermoresponsive aggregation/dispersion in heating/cooling thermal cycles through the LCST.

Poly ( α -hydroxy ethylene oxide-co- β -benzyl l -aspartate), α -hydroxy PEO/PBLA, block copolymers were used for the formulation of new functional polymeric micelles. They have a small diameter (about 30 nm) and a very low critical micellar concentration (cmc) in water, ca. 4 mg l −1 . Doxorubicin (DOX) was physically entrapped into the hydrophobic inner core of these functional micelles. The diameter of DOX-loaded α -hydroxy PEO/PBLA micelles was determined to be approximatively the same as the diameter of the corresponding empty micelles, ca. 25 nm. Moreover, the DOX-loaded functional micelles, as the corresponding empty micelles, were shown to be stable in 0.1 M phosphate buffered solution (PBS) pH 7.4 even in presence of proteins. The cytotoxicity of DOX-loaded functional micelles against P388D1 leukemia cells was studied and compared to the one of DOX-loaded α -methoxy PEO/PBLA micelles and to the cytotoxicity of both α -hydroxy and α -methoxy PEO/PBLA micelles. From this study it was concluded that the DOX-loaded functional micelles seem to have a slightly higher cytotoxicity than the DOX-loaded α -methoxy PEO/PBLA micelles, while both empty micelles were shown to be non-cytotoxic against P388D1 leukemia cells.

Purpose. To design glucose-responsive gels based on the complexation between polymers having phenylboronic acid groups and poly (vinyl alcohol). Specifically, high-glucose sensitivity at physiological pH was achieved through the interaction of phenylborate with amino groups.

The synthesis and characterization of comb-type grafted thermo-sensitive hydrogels is presented. These hydrogels were synthesized by polymerization of N-isopropylacrylamide (IPAAm) with a PIPAAm macromonomer. This process leads to a crosslinked IPAAm backbone polymer, copolymerized with highly mobile comb-type PIPAAm chains. These new thermo-responsive copolymers displayed higher equilibrium swellings at lower temperatures and rapid deswelling kinetics at elevated temperatures. The swelling/deswelling for comb-type gels is dependent on the graft chain lengths, in contrast to normal PIPAAm gel lacking the graft chains. As the temperature is increased above the critical temperature, the dehydrated graft chains aggregated due to hydrophobic attraction. Rapid and reversible kinetics of the graft-type gel were observed in response to stepwise temperature changes within short time cycles: phenomena not observed in normal crosslinked thermo-sensitive gels. The influence of freely mobile graft chains on both the equilibrium and dynamic properties of comb-type PIPAAm gel is demonstrated. Possible application of graft-type gel is discussed for actuator systems.

Glucose-Sensitive Lower Critical Solution Temperature Changes of Copolymers Composed of N -Isopropylacrylamide and Phenylboronic Acid Moieties

We have prepared a copolymer containing both phenylboronic acid and tertiary amine moieties. The copolymer forms a stable complex with poly(vinyl alcohol) (PVA) since boronate moieties interact with PVA hydroxyl groups. The polymer-polymer complex changes its swelling degree with glucose concentration in Dulbecco's phosphate-buffered saline solution (PBS) at pH 7.4, due to the higher complex formation of boronic acid moieties with glucose hydroxyl groups over those in PVA. Glucose-responsive swelling changes of a membrane complex were then utilized to control glucose-responsive current changes with a membrane-coated platinum electrode. Glucose addition to PBS induces swelling of the cast gel membrane, leading to increased diffusion of ion species and thus increased measurable current changes. Since the addition of methyl α-d-glucoside has little influence on the current changes, the current change by the addition of glucose is indicative of the high selectivity of this system for glucose and its cis-hydroxyl groups in glucose. It is observed that current changes are proportional to glucose concentration in the range 0-300 mg/dL. This range corresponds well to physiological blood glucose levels. Current change rates determined from the slope of the time course immediately after glucose addition are also proportional to glucose concentration within this range, yielding even higher sensitivity to the change in glucose concentration. Reproducible signal output is also demonstrated by repetitive, stepwise glucose concentration changes. These results support the applicability of the platinum electrode coated with the gel membrane complex comprising a phenylboronic acid-containing polymer and PVA for a novel glucose-sensing device.

Polymer-enzyme hybrid conjugates modified by a temperature-responsive polymer, poly(N-isopropylacrylamide) (PIPAAm), have been synthesized. We have investigated the molecular architecture of PIPAAm-enzyme conjugates by preparing two types of PIPAAm-trypsin conjugates, wherein PIPAAm chains are attached by either single-end or multipoint chemistry. A semitelechelic co-oligomer (IDc) was attached to trypsin by single-point conjugation (IDc-trypsin). A copolymer (PIDAAc) consisting of acrylic acid and IPAAm randomly linked in polymer chains was attached to trypsin using multipoint conjugation (PIDAAc-trypsin). Both conjugates exhibited reversible temperature-responsive phase separation. The IDc-trypsin conjugate exhibited phase separation at the same temperature as pure IDc, due to the highly mobile free polymer end group which remains sensitive to small temperature changes. The PIDAAc-trypsin conjugate precipitated at higher temperatures than pure PIDAAc, whose movement was restricted by multiple binding points. Enzyme stability in solution was improved after introduction of PIPAAm chains, which prevented autolysis attributed to conjugate steric hindrance. Stability under repeated temperature cycling was also dependent on the architecture of conjugates; the IDc-trypsin conjugate was more stable than the PIDAAc-trypsin. As a consequence, single-end conjugation of polymer to enzyme provides novel bioconjugate with novel functionality attributed to attached polymer while retaining native biological function with high stability.

Amino semitelechelic poly(N-isopropylacrylamide)s (PIPAAm) with three different molecular weights were synthesized by telomerization of IPAAm monomer with 2-aminoethanethiol as a chain transfer agent, changing the molar ratio of monomer to chain transfer agent. Macromonomers of thermosensitive PIPAAm were synthesized by condensation reaction of amino semitelechelic PIPAAm with N-acryloxysuccinimide. The molecular weights of macromonomers determined by titration of the terminal amino groups were 2900, 4000, and 9000, respectively. The comb-type grafted PIPAAm hydrogels having different lengths of graft chains were synthesized by radical copolymerization of IPAAm monomer with PIPAAm macromonomer in the presence of N,N'-methylenebisacrylamide as a cross-linker. An important aspect of the graft-type gels is the construction of a molecular architecture different from PIPAAm normal type ofgel even though the composition is same. Higher equilibrium swellings at lower temperatures were observed in graft-type gels in contrast to the normal-type gel, and longer graft chains resulted in higher equilibrium swelling due to the freely mobile grafted chains. Both the normal-type and the graft-type gels exhibited reversible swelling-deswelling changes in aqueous milieu in response to an alteration of temperature. The deswelling kinetics at 40 °C changed from equilibrium swelling states at 10 °C, however, exhibited remarkable differences, and rapid responses were observed for graft-type gels. The rapid dehydration of graft chains during gel shrinking was confirmed by analysis of DSC measurements. These dehydrated graft chains strongly aggregated with hydrophobic intermolecular forces, inducing the rapid deswelling of the gels. The attractive forces operating between dehydrated chains were larger in the gel having longer grafted chains, resulting in faster deswelling. A deswelling mechanism distinct from polymer network collective diffusion was demonstrated with these comb-type grafted hydrogels having freely mobile grafted chains in the network.

The electro-osmotic velocity has been measured on a poly( N -isopropylacrylamide) hydrogel plate at various temperatures. The results are analyzed on the basis of a theory for the electro-osmosis on a "soft" surface (i.e., a polyelectrolyte-coated surface) to determine the charge density and the "softness" of the hydrogel layer. It is found that as the temperature is raised, the charge density increases and the softness of poly( N -isopropylacrylamide) hydrogel decreases. These changes are most remarkable around 33°C. This is probably because poly( N -isopropylacrylamide) hydrogel shrinks above its LCST (33°C) and swells below it. This behavior is in good agreement with our previous results obtained from electrophoretic mobility measurements for poly ( N -isopropylacrylamide)-coated latex particles. The obtained values of the charge density in the hydrogel layer are compared with those that are estimated by potentiometric titration and the swelling ratio measurement of the hydrogel plate. Agreement is excellent, suggesting that the electro-osmosis measurements should be appropriate for analyzing the physicochemical properties of a soft surface.

Our research is directed toward development and fundamental studies of biomedically relevant modulation systems using the temperature-responsive polymer, poly(N-isopropylacrylamide) (PIPAAm) functionalized with a carboxyl end group, as the switching element. This material has been attached to both biomolecules and solid surfaces to create new, modified bioconjugates and grafted surfaces, respectively. PIPAAm was used to introduce a reversible switching function correlated to hydration-dehydration changes of polymer chains in response to changes in temperature. The introduction of PIPAAm chains onto polymer surfaces is intended to impart temperature-responsive surface property changes. These surfaces were prepared using either PIPAAm with a terminal carboxyl end group or random copolymers of PIPAAm with acrylic acid. The effects of graft conformation on the dynamics of grafted PIPAAm species were investigated by means of aqueous dynamic contact angle measurement. Each PIPAAm-grafted surface showed completely hydrophilic nature below 20°C, however, these surfaces become hydrophobic above their critical temperature. The extent of hydrophobic property for multipoint-grafted surfaces was small compared to that of the terminally grafted surface. These hydrophilic/hydrophobic surface property changes affect the platelet contact activation. The increase in cytoplasmic [Ca2+]i in platelets was observed only when PIPAAm grafted surface become hydrophobic. The feasibility of cell activation/inactivation control by temperature-modulated surface changes is attractive as modulator for biomedical systems and this strategy may lead to development of new ‘intelligent materials' with specific temperature-modulated surface properties.

Temperature-responsive poly( N -isopropylacrylamide) and its copolymer gels with the hydrophilic comonomer, acrylamide and the hydrophobic comonomer, butyl methacrylate, all exhibit swelling-deswelling changes in response to external temperature changes. These hydrogels show negative swelling thermosensitivities, particularly swelling at lower temperature and complete deswelling over specific phase transition temperatures ( T p ). Shrinking kinetics of these gels from swollen to deswollen states at several different temperature changes have been investigated. When temperature changes are performed entirely below T p , the shrinking process is dominated by polymer network diffusion. On the other hand, shrinking kinetics for temperature changes from below to above T p , are dramatically influenced by gel surface structural changes and formation of a collapsed polymer skin layer. This surface skin formation prompts the accumulation of internal hydrodynamic pressure inside the gels upon shrinking by blocking the outflux of entrapped water. Both rate and magnitude of internal hydrodynamic pressure are modulated by the gel volume, the hydrophobicity of the gel polymer chains and the degree of external temperature changes. This internal pressure eventually causes convective outflow of water from the gel interior. Hydrodynamic internal pressure affects the drug release on-off pattern during gel shrinking.

The influence of adsorbed plasma proteins on preventing contact-induced activation of platelets on poly(propylene oxide) (PPO)-segmented nylon-610 surfaces was investigated by monitoring changes in cytoplasmic free Ca2+ concentrations in platelets and adsorption/desorption of albumin and fibrinogen on these copolymer surfaces. Direct measurement of cytoplasmic free Ca2+ concentration in platelets in contact with copolymer surfaces was achieved by monitoring spectral changes of a fluorescent indicator dye, Fura 2. These copolymers were characterized by a surface microstructure composed of coexisting crystalline and amorphous phases. An increase in cytoplasmic free Ca2+ concentration in platelets interacting with polymer surfaces was observed, and this increase was found to be strongly reduced both by the adsorption of plasma proteins into the polymer surface and by modifying the surface microstructure of the polymer itself. Transient changes in cytoplasmic free Ca2+ concentration were observed in platelets in contact with the surface of copolymer 61P3-25, which exhibited excellent nonthrombogenicity in our previous studies, depending on the residence time of plasma and plasma concentration. Additionally, adsorption/desorption of albumin and fibrinogen on copolymer surfaces was estimated using 125I-labeled proteins. Exchange of the adsorbed albumin with fibrinogen and minimum fibrinogen adsorption were observed particularly on the 61P3-25 surface. Exchange of adsorbed fibrinogen with plasma proteins and/or increased fibrinogen adsorption were also observed on all other polymer surfaces examined. Finally, we conclude that controlled formation of a defined protein adsorption layer on the 61P3-25 surface via the transient exchange of adsorbed albumin with fibrinogen from plasma, can be a dominant factor in preventing platelet adhesion and activation on this surface.

The conjugation reaction of adriamycin (ADR) to poly (ethylene oxide)-poly (aspartic acid) block copolymer (PEO-P(Asp)) was optimized in order to inhibit side reactions, which damage the ADR residues. By diminishing alkaline components and lowering temperature, ADR was successfully conjugated to PEO-P(Asp) without side reactions. The obtained ADR-conjugated poly(ethylene oxide)-poly(aspartic acid) block copolymer [PEO-P(Asp(ADR))] was observed to form a micellar structure with a narrower distribution in size than the PEO-P(Asp(ADR)) synthesized by the previously reported method. Unconjugated ADR remained in the inner core of the PEO-P(Asp(ADR)) micelles was removed by dialysis in organic solvents to obtain the micelle without free ADR. Regulated amount of free ADR was then successfully entrapped into the inner core of these purified micelles. In vitro cytotoxicity against P388D1 cells of PEO-P(Asp(ADR)) micelle without free ADR was assayed to estimate the contribution of physically entrapped ADR on anti-tumor activity of the micelle-forming polymeric drug, PEO-P(Asp(ADR)).

We have investigated temperature modulation of surface properties for hydrophilic/hydrophobic changes using poly(N-isopropylacrylamide) (PIPAAm). Two types of PIPAAm were used as surface modifiers: an end-functionalized PIPAAm with a carboxyl end group and a poly(IPAAm-co-acrylic acid) copolymer. By means of dynamic contact angle measurements in water, the wettability of terminally polymer grafted surfaces using end-functionalized PIPAAm with a carboxyl end group were compared with that of multipoint polymer grafted surfaces using PIPAAm copolymers containing carboxyl groups along the polymer chain. Each PIPAAm grafted surface showed completely hydrophilic properties under 20 o C

Well-defined poly(ethylene oxide)s with a primary amino group at one end and a hydroxyl group at the other terminus were synthesized with new sila-protected amino functionality initiator, potassium N-[2-(2,2,5,5-tetramethyl-1-aza-2,5-disilacyclopentyl)-ethyl]methyl amide [1b]. 1b initiated an anionic polymerization of ethylene oxide (EO) to form a polymer (PEO) without any side reactions such as a cleavage reaction of protective group and a chain transfer reaction. The molecular weights of the PEO determined from GPC and MALDI TOF-MS spectrometry agreed well with those from end group analysis using 1H and 13C NMR and TLC and also with the expected value from EO/initiator ratio. From these results, it was concluded that the polymers thus obtained had a primary amino group at one end and a hydroxy group at the other end and can be regarded as hetrobifunctional PEO.

Temperature-responsive poly(N-isopropylacrylamide-co-butyl methacrylate) gels exhibit “on—off” regulation of drug release in response to temperature. In a previous study, swelling kinetics of these gels from deswollen to swollen states at several temperature were investigated. It was demonstrated that the swelling behavior of the gel changed at various temperatures, yielding several patterns of drug release profiles. At 20°C, gel swelling increased with time, which was explained using a Case-II transport mechanism. In this mechanism, the glassy polymer matrix core acts to suppress the swelling of the outer region when swelling forces dominate. By reducing the experimental temperature to 10°C and utilizing the greatly enhanced hydration of polymer chains after disappearance of the glassy core, a sigmodal swelling pattern gives rise to novel drug release profiles. In this study, these swelling mechanisms have been verified in detail by theoretical analysis. The existence of a swelling front was confirmed by observation of the colored gel using a dye. When the thickness of gel was changed, the acceleration of swelling was delayed with increasing thickness, and the acceleration times agreed with theoretical values predicted from the model. The observed changes in diameter and thickness of the gel also supported the model. This results demonstrate validity of the model presented with the previous paper.

Complex formation between PDMAAm as a hydrogen-bonding acceptor and PAAc as a hydrogen-bonding donor, the temperature dependence of the equilibrium swelling for IPN hydrogels composed of PDMAAm and PAAc, and changes in ketoprofen release of these IPN hydrogels were investigated. Interpolymer complexes between PDMAAm and PAAc were very stable at 70°C in aqueous solution. Dissociation temperatures of the complex between poly(DMAAm-co-AAm) and PAAc shifted to higher values with increasing DMAAm content. These IPNs composed of poly(DMAAm-co-AAm) and PAAc showed limited swelling ratios between their swelling transition temperatures and lower swelling ratios above these transition temperatures. Transition temperatures shift to higher values with increasing DMAAm content

Changes in platelet cytoplasmic free calcium levels were investigated in contact with cast film surfaces of a block copolymer containing 2-hydroxyethyl methacrylate (HEMA) and styrene (St) (0.5 mole fraction HEMA). These copolymer surfaces demonstrate microdomain alternating lamellae structures composed of hydrophilic HEMA domains (5 nm width) and hydrophobic St domains (20 nm width). The results were compared with those obtained from platelets contacting a random copolymer of HEMA-St (0.5 mole fraction HEMA) and from homopolymers of polystyrene (PSt) and poly(2-hydroxyethyl methacrylate) (HEMA). Cytoplasmic free calcium levels in platelets contacting the microdomain structured surfaces of the HEMA-St block copolymer remained relatively constant in contrast to the significant increases observed for the radically prepared HEMA-St copolymer, PSt, and PHEMA surfaces. Adhering platelets were stimulated by exogenously introduced thrombin and calcium ionophore A23187 20 min after platelet adherence to the polymer surfaces. Only platelets on the block copolymer surfaces showed active metabolic responses. These results suggest that adhering platelets on the microdomain structured surfaces maintain high sensitivities to external stimulation due to an intrinsic strong inhibition of platelet functional changes induced by surface contact. © 1993 John Wiley & Sons, Inc.

Poly(N-isopropyl acrylamide) (PIPAAm) demonstrated a fully expanded chain conformation below 32 degrees C and a collapsed, compact conformation at high temperatures. This unique temperature responsive polymer was grafted onto surfaces of commercial polystyrene dishes and used as temperature switches for creating hydrophilic surfaces below 32 degrees C and hydrophobic surfaces above 32 degrees C. Cell attachment and the growth of bovine endothelial cells and rat hepatocytes on PIPAAm-grafted surfaces at 37 degrees C demonstrated similar behavior to the commercialized culture dishes. Both cell types were observed to detach from the PIPAAm-grafted surface simply by reducing the temperature below the polymer transition temperature (collapse). Cells recovered by this method maintained substrate adhesivity, growth, and secretion activities nearly identical to those found in primary cultured cells in contrast to the compromised function found in cultured cells damaged by trypsinization. These results provide strong evidence that PIPAAm-grafted surfaces, as thermal switches are very effective for reversing cell attachment and detachment without cell damage. Properties of cell culture surfaces can be readily transformed by this technique reversibly into hydrophilic and hydrophobic coatings of PIPAAm-grafted polymers.

The micelle-forming behavior of a drug–block copolymer conjugate adriamycm-conjugated poly(ethylene glycol)–poly(aspartic acid) block copolymer; PEG-P[Asp(ADR)] was analyzed by gel permeation chromatography (GPC). Four compositions of the conjugates were observed to form micellar structures in aqueous media, and their micelle-forming behavior was found to be dependent on the composition and media. These micelles did not reach equilibrium within short time periods like low molecular weight surfactants. One composition formed stable micelles in the presence of serum.

Thermoresponsive poly(N-isopropylacrylamide-co-alkyl methacrylate) gels are capable of on-off regulation of drug release in response to external temperature changes because a gel surface skin formed with increasing temperature stops drug release from the gel interior. In this gel shrinking process, observation of bubble formation on the surface indicates that pressure is induced within the gel. This pressure may result in an outward convection of water

Adriamycin, a hydrophobic anticancer drug, was conjugated with poly(ethylene oxide)-poly(aspartic acid) block copolymers composed of various lengths of each block copolymer segment ranging from 1000 to 12,000 in molecular weight and from 10 to 80 units, respectively. Conjugation was achieved without precipitation by adjusting the ratio of adriamycin to aspartic acid residues of the block copolymer and the quantity of DMF used for the reaction. Thus obtained conjugates showed high water solubility irrespective of a large amount of the conjugated adriamycin. Furthermore, these conjugates were found to form micellar structures with a hydrophobic inner core and a hydrophilic outer shell. This micellar architecture may be utilized for effective drug targeting.

A novel polymer complex system sensitive to glucose was studied as a candidate material for formulating a chemically regulated insulin delivery system. A phenylboronic acid (PBA) moiety was incorporated in poly(N-vinyl-2-pyrrolidone) [poly(NVP-co-PBA) ] as a glucose sensor molecule by the radical copolymerization of N-vinyl-2-pyrrolidone with m-acrylamidophenylboronic acid. Complex formation as well as dissociation was estimated by viscosity changes in the complex solution. A positive viscosity change was observed for the poly (vinyl alcohol) (PVA)/poly(NVP-co-PBA) complex system due to complex formation between PVA diol units and poly(NVP-co-PBA) boronate units; minimal or no change in viscosity was observed for either PVA/boric acid or PVA/poly(NVP). The viscosity of the PVA/poly(NVP-co-PBA) system is able to be controlled through changes in polymer molecular weight and/or polymer concentration. The maximum point in viscosity was observed at a molar ratio of PVA to poly (NVP-co-PBA) of 4:1 in this system. The diol-boronate complex interaction was further investigated by following decreased complex viscosity with the addition of a competitive polyol: glucose, tris(hydroxymethyl)aminomethane (TRIS) or (±)-3-amino-1,2-propanediol (APD). The viscosity decreased steeply when glucose was added while minimal change in viscosity was observed when either TRIS or APD was added. This suggested that the chemical structure of the diol compound had an important role in exchange with the diol-boronate complex. These results point to the promising use of PVA/poly(NVP-co-PBA) complex systems in the development of a novel glucose responsive insulin release system.

Thermosensitive co-polymers of isopropyl acrylamide (IPAAm) with butyl methacrylate (BMA) are capable of 'on-off' regulation of drug release in response to external temperature changes due to skin formation with increasing temperature. To clarify the role of the surface-modulated skin and controlled pulsatile drug release patterns, the surface shrinking process was regulated by changing the length of the methacrylate alkyl side-chain. Release of indomethacin in response to stepwise temperature changes between 20 and 30 degrees C from co-polymers of IPAAm with BMA, hexyl methacrylate (HMA), and lauryl methacrylate (LMA) was studied. The drug release rate during the 'on' state (20 degrees C) remained constant before and after the 'off' state (30 degrees C) when the period of the 'off' state was increased. These results suggest that the drug in the polymeric matrices diffused from the inside to the surface during the 'off' state even when no drug release was seen. The length of alkyl side-chain was found to be an important parameter in controlling the thickness and density of the surface skin layer.

New concept of inflammation responsive drug delivery system by biodegradable hydrogels of hyaluronic acid (HA) is reviewed. HA has been well known to be degraded specifically by the presence of hydroxyl radicals, which are produced locally at an inflammatory site. Our system is established by constructing a heterogeneous-structured device of drug microreservoirs (lipid microspheres) dispersed into the degradable matrices of crosslinked HA gel. The most attractive characteristics of this device are : (1) to performe the release of lipid microspherers in proportion to surface-controlled degradation of crosslinked HA gels, and (2) to be quantitatively inflammation-responsive degradable. These unique features of the device are favorable to regulated drug delivery to several inflammatory related diseases, where lipid microspheres can be released in response to inflammation-induced degradation although being stable under normal health conditions.

A novel polymer complex system sensitive to glucose was studied as a candidate material for formulating a chemically regulated insulin release system. A ternary copolymer of N-vinyl-2-pyrrolidone (NVP), 3-acrylamidophenylboronic acid (AAm-PBA) and N,N-dimethylaminopropylacrylamide (DMAPAA) (poly(NVP-co-PBA-co-DMAPAA)) was synthesized by radical copolymerization. The phenylboronic acid group in this copolymer serves as a glucose sensor moiety. Poly(NVP-co-PBA-co-DMAPAA) was soluble in water in the pH range of 3–12, in sharp contrast to a binary copolymer of NVP and AAm-PBA (poly(NVP-co-PBA)) which showed solubility only under alkaline aqueous conditions, where the boronic acid group is in a tetrahedral ionized form. The protonated amino group in poly(NVP-co-PBA-DMAPAA) contributed to increase the solubility of the polymer under physiological and acidic aqueous conditions. Furthermore, poly(NVP-co-PBA-co-DMAPAA) formed a stable polymer complex gel with poly(vinyl alcohol) (PVA) in pH 7.4 phosphate buffered solution due to the formation of a covalent linkage between the boronic acid groups in ternary copolymer and diol units in PVA. The release of myoglobin as model protein from the complex gel was increased immediately after the addition of glucose, due to the transition of gel into sol state, indicating the feasibility of this complex gel as a candidate material for a glucose-responsive delivery system for insulin.

Interpenetrating polymer networks (IPNs) composed of poly(acrylamide(AAm)-co-butyl methacrylate (BMA)) and poly(acrylic acid) (PAAc) demonstrate positive swelling changes with an abrupt transition as temperature increases. Temperature-modulated controlled drug release using swelling-shrinking responses of the hydrogels as on-off switches for drug release is reported. The IPNs demonstrate “on” release at higher temperatures. When changing from higher to lower temperatures, an immediate pulsatile drug release is observed followed by a nearly complete “off” state of drug release. The drastic increase of drug release rate is due to mechanical squeezing by a shrinking gel surface layer of the IPNs in response to decreasing temperature. The following decrease of drug release is due to a subsequent formation of a dense layer of polymer at the IPN surface.