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A mechanism on why slower polymerization of a dental composite produces lower contraction stress.

It has been well documented that the rate of polymerization of a dental composite often affects its polymerization contraction stress. In most cases, a slower cure produces a lower stress. To investigate the mechanism behind this, we prepared an unfilled dimethacrylate resin sample and photocured it using two light irradiances, both with the same total irradiation energy. We measured the polymerization-induced shrinkage from the unbonded surface of a class I restoration, contraction stress, extent of polymerization, and flexural modulus. The resin specimens cured under the two irradiances achieved the same extent of polymerization and developed an identical amount of shrinkage from the unbonded surface. But those cured under the lower irradiance possessed a lower contraction stress and a lower flexural modulus than those cured under the higher irradiance. We demonstrated that the stress level did not respond to the extent of viscous flow of the curing resin because the slower polymerization did not produce more shrinkage from the unbonded surface. Instead, the lower stress is likely due to a lower modulus of the cured resin. To explain why the cured resin with an identical extent of polymerization can have different moduli, we proposed that slower polymerization produces a higher level of structural inhomogeneity, which reduces the rigidity of the cured resin.

Calorimetry, Differential Scanning↗

Role of cysteine-291 and cysteine-322 in the polymerization of human tau into Alzheimer-like filaments.

Filamentous tau pathology is central to a large number of dementing disorders, including Alzheimer's disease in which polymerized tau is hyperphosphorylated. Previous studies on heparin-dependent tau polymerization, using recombinant tau isoforms lacking Cys-291, suggest that tau dimerization via Cys-322 is critical for initiation of assembly of soluble tau into filaments. We report heparin-dependent in vitro polymerization of human recombinant tau (1-383 isoform), containing both Cys-291 and Cys-322, into paired helical filaments as characterized by electron microscopy. Tau polymerization, under physiological tau concentrations in the presence of dithiothreitol (DTT), was followed by a Thioflavine S fluorescence assay. To understand the molecular basis for heparin-induced tau polymerization, we expressed and purified C291A, C322A, and C291A/C322A tau mutants. The DTT requirement for tau polymerization was abolished using either the C291A or C322A tau mutant and polymerization was not observed with the C291A/C322A tau double mutant. Analysis by sodium dodecyl sulfate gel electrophoresis showed that, unlike wild type tau, a significant amount of the C291A mutant and the C322A mutant is present as a disulfide bonded dimer. Taken together these results suggest that, in isoforms containing both Cys-291 and Cys-322, a dimeric tau with an intermolecular disulfide bond through either Cys-291 or Cys-322 is presumably acting as a seed for initiation of tau polymerization.

Alzheimer Disease↗

The rate of polymerization of rabbit skeletal muscle actin is enhanced by polyethylene glycol.

The effect of polyethylene glycol on the kinetics of actin polymerization was determined by monitoring the enhancement in the fluorescence of pyrenyl-labelled actin. The polymerization of actin at 15 mM KCl was in addition followed by viscometry and light scattering. All three methods showed that the overall rate of polymerization of actin increased 3-4-fold when the concentration of polyethylene glycol was increased from 0 to 6% (ww-1). A further increase in polyethylene glycol concentration to 10% (ww-1) caused a relatively small contribution to the increase in the rate of polymerization. The enhancement of the overall rate of polymerization by polyethylene glycol was also reflected in a significant decrease in the lag time observed when the time course of polymerization was followed by viscometry and light scattering. The steady-state value of fluorescence enhancement and critical concentration of actin were also influenced by polyethylene glycol and the results showed that the extent of polymerization was increased by an increase in the concentration of polyethylene glycol in solution. The effect of polyethylene glycol on both rate and extent of polymerization persisted at physiological salt concentration (150 mM KCl, 2 mM MgCl2). Since the rate of elongation was affected only to a small extent by polyethylene glycol, we propose that its main effect is on nucleation.

Actins↗

Magnesium reduces nickel inhibition of DNA polymerization.

The activities of DNA polymerization and DNA ligation in extract of Chinese hamster ovary cells were both stimulated by MgCl2. DNA polymerization was stimulated by MgCl2 above 0.25 mM, whereas, MgCl2 above 2 mM was required to stimulate DNA ligation. The activity of DNA polymerization maintained a plateau at MgCl2 1-12 mM, whereas DNA ligation reached a maximal activity at MgCl2 6 mM and decreased thereafter. NiCl2 0.1-0.2 mM also had a stimulatory effect on DNA polymerization, but was much less potent than MgCl2. However, nickel ion (Ni2+) had no detectable stimulating effect on the activity of DNA ligation. In the presence of MgCl2, the activities of DNA polymerization and DNA ligation decreased with increasing concentration of NiCl2. Ni2+ inhibition of DNA polymerization was reduced by increasing the concentration of MgCl2, but increasing the concentration of MgCl2 did not reduce Ni2+ inhibition of DNA ligation. Preincubating cell extract with MgCl2 decreased the Ni2+ inhibition of DNA polymerization but not DNA ligation. These results suggest that Ni2+ may compete with magnesium ion (Mg2+) to reduce DNA polymerization, but this mechanism seems not applicable to Ni2+ inhibition of DNA ligation.

Animals↗

An investigation of the antitumour activity and biodistribution of polymeric micellar paclitaxel.

PURPOSE: To evaluate in vitro cytotoxicity, in vivo antitumour activity and biodistribution of a novel polymeric (poly(DL-lactide)-block-methoxy polyethylene glycol) micellar paclitaxel. METHODS: Hs578T breast, SKMES non-small-cell lung, and HT-29 colon human tumour cells were exposed, either for 1 h or continuously, to conventionally formulated paclitaxel (Cremophor paclitaxel) or polymeric micellar paclitaxel. After a period of incubation, cytotoxicity was measured using a radiometric system. In the in vivo antitumour study, B6D2F1 mice, bearing P388 leukaemia tumour intraperitoneally (i.p.), were treated with polymeric micellar paclitaxel or Cremophor paclitaxel by i.p. injection. The number of deaths and body weights were recorded. In the biodistribution study, CD-1 mice were given micellar paclitaxel i.p. at a dose of 100 mg/kg. The mice were sacrificed after a given time and the organs were harvested. Paclitaxel in the organs was extracted by acetonitrile and analysed using HPLC. RESULTS: The polymeric micellar paclitaxel showed similar in vitro cytotoxicity to Cremophor paclitaxel against the tumour cell lines. The polymeric micellar formulation of paclitaxel produced a fivefold increase in the maximum tolerated dose (MTD) as compared with Cremophor paclitaxel when administered i.p. In addition, micellar paclitaxel was more efficacious in vivo when tested in the murine P388 leukaemia model of malignancy than Cremophor paclitaxel when both were administered i.p. at their MTDs. Micellar paclitaxel-treated animals had an increased survival time and, importantly, long-term survivors (20% of those tested) were obtained only in the polymeric paclitaxel formulation group. Biodistribution studies indicated that a significant amount of paclitaxel could be detected in blood, liver, kidney, spleen, lung and heart of mice after i.p. dosing of the polymeric micellar paclitaxel formulation. CONCLUSION: These preliminary results indicate that polymeric micellar paclitaxel could be a clinically useful chemotherapeutic formulation.

Animals↗

Assessment of microtubule stabilizers by semiautomated in vitro microtubule protein polymerization and mitotic block assays.

Paclitaxel (Taxol) a clinically active anticancer agent, exerts its cytotoxicity by inducing tubulin polymerization, leading to cellular mitotic block. In contrast, other antimitotic drugs, such as colchicine, podophyllotoxin, and vinblastine, act by depolymerizing microtubules. We report here (a) a semiautomated assay which measures the tubulin-polymerizing activity of paclitaxel analogs and (b) a cellular assay to measure the potential of these compounds to block cells in mitosis. The microtubule-polymerizing assay measured the turbidity of bovine brain microtubule protein (MTP) polymerized by the test compound in a 96-well plate. We maximized the sensitivity of this assay by conducting the polymerization reaction at 20 degrees C, at which temperature the baseline reaction, i.e. the basic ability of the untreated MTP control to polymerize, was minimal. At 20 degrees C, the effect of 0.05 microg/ml of paclitaxel on MTP could be detected, whereas at 37 degrees C, > 1 microg/ml of paclitaxel was required to detect a significant effect relative to untreated MTP. We describe the analysis of the complex curves of MTP polymerization with varying concentrations of test compounds. The polymerization of microtubules leads to cells being blocked in mitosis. This mitotic blocking effect in intact cells was determined using a cell settling chamber which allowed eight samples to be deposited on a slide. This method required a smaller number of cells (10(3) - 10[5]), maintained cell morphology, and allowed for rapid screening of samples. The activity of several new paclitaxel analogs is reported.

Animals↗

Curing efficiency of different polymerization methods through ceramic restorations.

The aim of this in vitro study was to examine the curing efficiency of three different polymerization methods through ceramic restorations by determination of the depth of cure and the universal hardness of a composite resin luting material. Therefore, 36 ceramic specimens [Empress 2 (Ivoclar), color 300, diameter 4 mm, height 2 mm] were prepared and inserted in steel molds (diameter 4 mm, height 6 mm) using a composite resin luting material [Variolink II (Vivadent)] with and without catalyst. The polymerization through six specimens of each group was done conventionally (40 s), by softstart polymerization (40 s), or by plasma arc curing (10 s). Depth of cure under the ceramic specimens was assessed according to ISO 4049. Additionally, universal hardness was determined at 0.5 and 1.0 mm from the ceramic using a universal testing machine (Zwick 14040). Curing without a catalyst, using conventional and softstart polymerization, resulted in greater hardness in both layers, compared to plasma arc curing. The use of a catalyst always produced a greater hardness and depth of cure with all polymerization methods. Depth of cure was always greater using conventional polymerization and softstart polymerization, compared to plasma arc curing. The curing efficiency of plasma arc curing through ceramic was lower compared to conventional and softstart-polymerization.

Dental Porcelain↗

Actin polymerization in cellular oxidant injury.

Microfilaments undergo an ATP-dependent disruption into shortened bundles following cellular exposure to oxidants. This phenomenon does not require a net change in the amount of polymerized actin. However, increased amounts of polymerized actin have been detected in oxidant-injured cells and it was the purpose of this study to determine the conditions under which the actin polymerization may occur. Utilizing the formation of oxidized glutathione (GSSG) as an indicator of cellular sulfhydryl oxidation, conditions were chosen to accentuate sulfhydryl oxidation within the target P388D1 cell line following exposure to the oxidants, H2O2 and diamide. Using the DNase I and flow cytometric assays of actin polymerization, significant polymerization of actin was detected only under conditions in which sulfhydryl oxidation occurred after exposure to the two oxidizing agents. Greater sulfhydryl oxidation early in the course of injury was associated with a greater rate and extent of actin polymerization in the injured cells. Experiments with cells depleted of glutathione (GSH) demonstrated that neither loss of GSH nor absolute levels of GSSG formed during oxidant exposure were responsible for the polymerization of actin. The data presented are consistent with the hypothesis that oxidizing conditions which induce significant sulfhydryl oxidation in target cells are correlated with assembly of polymerized actin and that this represents a process which is distinct and separate from the ATP-dependent gross disruption of microfilaments.

Actins↗

Insertion of bacteriorhodopsin into polymerized diacetylenic phosphatidylcholine bilayers.

We have developed a method to incorporate the membrane protein bacteriorhodopsin into polymerized bilayers composed of a diacetylenic phosphatidylcholine, 1,2-bis(tricosa-10,12-diynoyl)-sn-glycero-3-phosphocholine (DC8,9PC) and a non-polymerizable phospholipid, dinonanoylphosphatidylcholine (DNPC). The extent of DC8,9PC polymerization in the bilayer was significantly improved when 2:1 mole ratio DNPC-DC8,9PC was used. Octyl glucopyranoside-solubilized bacteriorhodopsin was inserted into the polymerized DNPC-DC8,9PC bilayers by overnight incubation at 4 degrees C followed by dialysis to remove the detergent. The protein was inserted into the membranes after photo-polymerization to avoid inactivation of the protein due to the UV irradiation. The insertion of bacteriorhodopsin into the polymerized DNPC-DC8,9PC membranes was confirmed by density gradient centrifugation, UV/visible spectroscopy, and freeze fracture electron microscopy. The polymerized DNPC-DC8,9PC membranes containing bacteriorhodopsin were about 10% protein by weight. These results suggest that mixed lipid systems such as the DNPC-DC8,9PC can be used to improve both the extent of polymerization and the efficiency of membrane protein incorporation in the polymerized bilayer.

Bacteriorhodopsins↗

Study of protein binding to a silica support with a polymeric cation-exchange coating.

A silica-based, polyacrylate ion-exchange stationary phase has been prepared using Ce(IV) as the initiator. Analysis of the physical properties of the polymeric layer separated from the silica surface indicates that the polymeric coating is cross linked to some extent. The polymerization carried out at different concentrations of Ce(IV) demonstrated that the effective surface area can be increased by lowering the Ce(IV) concentration at higher monomer concentrations of the reaction mixture. These materials are quite reproducible and of high electrostatic binding capacity; 1.485 mumol/m2. The electrostatic binding capacity of a non-polymeric stationary phase reached the theoretical limit for a monolayer (0.16 mumol/m2). However, the covalent binding capacity of the same stationary phase was only 50% of the electrostatic binding capacity. The same trend was observed in all the polymeric stationary phases tested. This shows that the mechanism of protein binding in polymeric and conventional stationary phases is similar, and multilayer electrostatic binding is highly unlikely in these sorbents examined. Z numbers revealed that the contact area of the protein is independent of the polymeric character of the stationary phase and therefore, the increased loading of these polymeric stationary phases is due to the increased surface area.

Acids↗

A simple method for determining polymeric IgA-containing immune complexes.

A simplified assay to measure polymeric IgA-immune complexes in biological fluids is described. The assay is based upon the specific binding of a secretory component for polymeric IgA. In the first step, multimeric IgA (monomeric and polymeric) immune complexes are determined by the standard Raji cell assay. Secondly, labeled secretory component added to the assay is bound to polymeric IgA-immune complexes previously fixed to Raji cells, but not to monomeric IgA immune complexes. To avoid false positives due to possible complement-fixing IgM immune complexes, prior IgM immunoadsorption is performed. Using anti-IgM antiserum coupled to CNBr-activated Sepharose 4B this step is not time-consuming. Polymeric IgA has a low affinity constant and binds weakly to Raji cells, as Scatchard analysis of the data shows. Thus, polymeric IgA immune complexes do not bind to Raji cells directly through Fc receptors, but through complement breakdown products, as with IgG-immune complexes. Using this method, we have been successful in detecting specific polymeric-IgA immune complexes in patients with IgA nephropathy (Berger's disease) and alcoholic liver disease, as well as in normal subjects after meals of high protein content. This new, simple, rapid and reproducible assay might help to study the physiopathological role of polymeric IgA immune complexes in humans and animals.

Antigen-Antibody Complex↗

Assays for total and antigen-specific polymeric IgA in serum based on binding to secretory component.

Binding assays with secretory component (SC) were used to detect polymeric IgA antibody to E. coli lipopolysaccharide and to estimate total polymeric IgA in sera from 14 patients with alcoholic liver disease and eight normal controls. Radioiodinated human SC was shown to bind to polymeric IgA and IgM but not to monomeric IgA, secretory IgA or IgG. Serum aliquots (0.5 ml) were totally depleted of IgM using 2 ml anti-IgM affinity columns and the effluent sera were titrated in microtitre plates coated with lipopolysaccharide, the binding of polymeric IgA being detected by adding 10 ng radiolabelled SC. Total polymeric IgA was measured via its capacity to inhibit the binding of 5 ng labelled SC to IgM coated wells, quantitation being achieved by comparison with the inhibition produced by purified polymeric IgA. Total lipopolysaccharide-specific IgA antibody was detected by ELISA in sera from both patients and controls, 1185 +/- 793 and 56 +/- 19 U/100 microliters (mean +/- SD), respectively; but polymeric IgA antibody was detected only in patients' sera (131 +/- 214 U/100 microliters). The concentration of total polymeric IgA was higher in patients' sera than in control sera (488 +/- 333 and less than 120 micrograms/ml respectively).

Antibodies, Bacterial↗

Polymerization and solubility of Ni(II)-Fe(II) hybrid Hb S.

Polymerization of half-liganded Hb S was investigated using Ni(II)-Fe(II) hybrid Hb S, in which heme in either alpha or beta s subunits is replaced by Ni (II) protoporphyrin IX. Studies on the polymerization of these hybrid hemoglobins were carried out under aerobic conditions. Both alpha 2 (Ni) beta 2s (Fe-CO) and alpha 2 (Fe-CO) beta 2s (Ni) polymerized with a distinct delay time as do native deoxy-Hb S and Ni(II) Hb S. However, the critical concentration for polymerization of half-liganded Hb S, alpha 2 (Ni) beta 2s (Fe-CO) and alpha 2 (Fe-CO) beta 2s (Ni), was 4- and 8-times higher, respectively, than that of Ni(II)-Hb S. Kinetics of polymerization of both deoxygenated hybrid hemoglobins with CO completely removed were the same, although the critical concentrations for polymerization were intermediate between those for deoxy-Hb S and Ni(II)-Hb S. These results suggest that the small tertiary conformational change associated with the doubly liganded state may be much less favorable to polymerization than the completely unliganded state of Hb S. The conformational change depends on whether alpha or beta chain is liganded. The ease of polymerization and low solubility of sickle hemoglobin is dependent not only on quaternary, but on tertiary structural changes, as well as on the substitution of Val for Glu at the beta 6 position.

Hemoglobin, Sickle↗

Promotion of microfilament polymerization by depolymerized glia filament preparation through interaction of vimentin with actin.

We investigated the in vitro interaction between microfilaments and glia filaments in the presence of alpha-sialosylcholesterol (SC). The depolymerized glia filament preparation (GF) that had been extracted from a crude cytoskeletal fraction of cultured rat astrocytes promoted markedly the polymerization of the depolymerized microfilament preparation (MF) in the presence of SC. The ability of GF to promote the MF polymerization was highest in the concentration range 7.5-15 microM SC. The polymerization of MF at the concentration of 10 micrograms protein/200 microliters was enhanced to the highest level by 4 micrograms protein/200 microliters of GF in the presence of 15 microM SC. The MF polymerization was promoted more efficiently by GF than by MF: for example, the polymerization of actin in MF (7.5 micrograms/200 microliters) was enhanced by the addition of 5 micrograms GF protein/200 microliters to a twice greater extent than by the addition of 5 micrograms MF protein/200 microliters in the presence of 15 microM SC. GF enhanced the MF polymerization by over three-fold at 4-37 degrees C, and the GF activity became greater with an increase in incubation temperature. Vimentin promoted the G-actin polymerization in the presence of 11.3 microM alpha-SC. The finding suggested that the interaction between vimentin and actin was one of the factors to cause GF to promote the MF polymerization.

Actin Cytoskeleton↗

Inhibition of tubulin polymerization with ribose-modified analogs of GDP and GTP. Reduced inhibition with microtubule-associated proteins and magnesium.

Inhibitory effects of ribose-modified GDP and GTP analogs on tubulin polymerization were examined to explore nucleotide structural requirements at the exchangeable GTP binding site. With microtubule-associated proteins and Mg2+, GTP-supported polymerization was only modestly inhibited by GDP, and still weaker inhibitory activity was found with two analogs, dGDP and 9-beta-D-arabinofuranosylguanine-5'-diphosphate (araGDP). Omission of Mg2+ significantly enhanced the inhibitory effects of GDP, dGDP and araGDP and resulted in weak inhibition of the reaction by several other GDP analogs. The relative inhibitory activity of the GDP analogs had no discernible relationship to the relative activity of cognate GTP analogs in supporting microtubule-associated protein-dependent polymerization. One GTP analog, 2',3'-dideoxyguanosine 5'-triphosphate (ddGTP), supports polymerization both with and without microtubule-associated proteins. The inhibitory activity of GDP and GDP analogs in ddGTP-supported polymerization was much greater in the absence of microtubule-associated proteins than in their presence; and both reactions were more readily inhibited than was microtubule-associated protein-dependent, GTP-supported polymerization. Microtubule-associated protein-independent, ddGTP-supported polymerization was also potently inhibited by GTP and a number of GTP analogs. GTP was in fact twice as inhibitory as GDP. The relative inhibitory activity of the GTP analogs was comparable to the relative inhibitory activity of the cognate GDP analogs and very different from their relative activity in supporting polymerization.

Animals↗

Pepstatin A: polymerization of an oligopeptide.

Pepstatin A, a pentapeptide with the molecular weight of 686, is a naturally occurring inhibitor of aspartyl proteases secreted by Streptomyces species. Above a critical concentration of 0.1 mM at low ionic strength and neutral pH, it can polymerize into filaments which may extend over several micrometers. After negative staining, these filaments show a helical substructure with characteristic diameters ranging from 6 to 12 nm. Selected images at higher magnification suggest the filaments are composed of two intertwined 6 nm strands. This is in agreement with the optical diffraction analysis which additionally established a periodic pitch of 25 nm for the helical intertwining. Rotary shadowing of the pepstatin A filaments clearly demonstrated the right-handedness of the helical twist. In physiological salt solution or at higher concentrations of pepstatin A, a variety of higher order structures were observed, including ribbons, sheets and cylinders with both regular and twisted or irregular geometries. Pepstatin A can interact with intermediate filament subunit proteins. These proteins possess a long, alpha-helical rod domain that forms coiled-coil dimers, which through both hydrophobic and ionic interactions form tetramers which, in turn, in the presence of physiological salt concentrations, polymerize into the 10 nm intermediate filaments. In the absence of salt, pepstatin A and intermediate filament proteins polymerize into long filaments with a rough surface and a diameter of 15-17 nm. This polymerization appears to be primarily driven by nonionic interactions between pepstatin A and polymerization-competent forms of intermediate filament proteins, resulting in a composite filament. Polymerization-incompetent proteolytic fragments of vimentin, lacking portions of the head and/or tail domain, failed to copolymerize with pepstatin A into long filaments under these conditions. These peptides, as well as bovine serum albumin, were found to stick to the surface of pepstatin A filaments, ribbons and sheets. Independent evidence for direct association of pepstatin A with intermediate filament subunit proteins was provided not only by electron microscopy but also by UV difference spectra. Pepstatin A loses its ability to inhibit the aspartyl protease of the human immunodeficiency virus type 1 following polymerization into the higher order structures described here. The amazing fact that pepstatin A can spontaneously self-associate to form very large polymers seems to be a more rare event for such small peptides. The other examples of synthetic or naturally occurring oligopeptides discussed in this review which are able to polymerize into higher order structures possess a common property, their hydrophobicity, often manifested by clusters of valine or isoleucine residues.(ABSTRACT TRUNCATED AT 400 WORDS)

Intermediate Filament Proteins↗

Organic plasma process for simple and substrate-independent surface modification of polymeric BioMEMS devices.

A polymeric bio micro electromechanical systems (BioMEMS) device was fabricated using organic plasma polymerization, by which the surface of a polymeric substrate could easily be modified through vapor-phase deposition of organic thin films. This technique, capable of polymeric deposition of any kind of monomer, can serve the purpose of anti-fouling coating, wettability control, or layer-to-layer interface creation, on the surface of any given chemically-inert polymeric substrate without involving cumbersome surface organic reactions. A prototype device was fabricated to have an array of electrochemical glucose biosensors with the three electrode configuration, each of which has a microfluidic channel (500 microm x 800 microm) for capillary-action-driven sample delivery and the concerned enzymatic reaction. Stressing the advantages of the plasma polymerization process using a polymeric substrate together with some additional features accomplished in our device fabrication, new possibilities in the field of polymeric BioMEMS are discussed.

Biosensing Techniques↗

Evidence that catalytically-inactivated thrombin forms non-covalently linked dimers that bridge between fibrin/fibrinogen fibers and enhance fibrin polymerization.

Phe-pro-arg-chloromethyl ketone-inhibited alpha-thrombin [FPR alpha-thr] retains its fibrinogen recognition site (exosite 1), augments fibrin/fibrinogen [fibrin(ogen)] polymerization, and increases the incorporation of fibrin into clots. There are two 'low-affinity' thrombin-binding sites in each central E domain of fibrin, plus a non-substrate 'high affinity' gamma' chain thrombin-binding site on heterodimeric 'fibrin(ogen) 2' molecules (gamma(A), gamma'). 'Fibrin(ogen) 1' (gamma(A), gamma(A)) containing only low-affinity thrombin-binding sites, showed concentration-dependent FPR alpha-thr enhancement of polymerization, thus indicating that low-affinity sites are sufficient for enhancing polymerization. FPR gamma-thr, whose exosite 1 is non-functional, did not enhance polymerization of either fibrin(ogen)s 1 or 2 and DNA aptamer HD-1, which binds specifically to exosite 1, blocked FPR alpha-thr enhanced polymerization of both types of fibrin(ogen) (1>2). These results showed that exosite 1 is the critical element in thrombin that mediates enhanced fibrin polymerization. Des B beta 1-42 fibrin(ogen) 1, containing defective 'low-affinity' binding sites, was subdued in its FPR alpha-thr-mediated reactivity, whereas des B beta 1-42 fibrin(ogen) 2 (gamma(A), gamma') was more reactive. Thus, the gamma' chain thrombin-binding site contributes to enhanced FPR alpha-thr mediated polymerization and acts through a site on thrombin that is different from exosite 1, possibly exosite 2. Overall, the results suggest that during fibrin clot formation, catalytically-inactivated FPR alpha-thr molecules form non-covalently linked thrombin dimers, which serve to enhance fibrin polymerization by bridging between fibrin(ogen) molecules, mainly through their low affinity sites.

Amino Acid Chloromethyl Ketones↗