Anticoagulant activity of a synthetic heparinoid in relation to molecular weight and <i>N</i>‐sulfate content

Sederel, L.C.; Does, L. van der; Duijl, J.F. van; Beugeling, T.; Bantjes, A.

doi:10.1002/jbm.820150606

Cited by 29 publications

(11 citation statements)

References 10 publications

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“…In group B there was significant C3bc activation by 34% from 11 (7)(8)(9)(10)(11)(12)(13)(14)(15) to 16 (8-24) AU/ml (p < 0.01), which was not significantly different from the 94% increase in the corresponding water-bath control samples (control B): 20 (12-32) AU/ml. In group C C3bc increased by 22% from 8 (6-11) to 10 (6-14) AU/ml (NS), which was significantly lower than the 54% increase in the corresponding water-bath control samples (control C): 13 (9-18) AU/ml (p < 0.01).…”

Section: C3 Complement Activation Productscontrasting

confidence: 50%

“…sulphonated polymers have a characteristic anticoagulant effect and sulphonation is intended to mimic the functional groups responsible for heparin' s anticoagulatory effect. 12,13 Therefore, the Avecor coating has incorporated a high degree of sulphate and sulphonate groups. The negative charge created by the sulphonate groups is also believed to have an effect on the thromboresistance of materials due to the electrical repulsion effects between negatively charged blood components.…”

Section: Introductionmentioning

confidence: 99%

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In vitro evaluation of new surface coatings for extracorporeal circulation

et al. 1999

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Cardiopulmonary bypass (CPB) exposes blood to large, foreign surfaces. This exposure may activate the cellular and humoral inflammatory systems, resulting in inflammatory reactions and organ dysfunction. Coating the inner surfaces of the bypass circuit may help alleviate these side-effects. The objective of this study was to determine the influence of two new surface treatments on blood cell and complement activation. Oxygenator and tubing sets coated with synthetic polymers (n = 7) or heparin (n = 7) were compared to uncoated sets (n = 7) in an in vitro model of CPB. The circuits were run at 4 l/min and recirculated for 120 min. The inflammatory response was assessed at regular intervals by platelet counts, and activation of complement, leucocytes and platelets. We found that the median platelet counts decreased from 127 to 122 x 10(9)/l (not significant, NS) in the synthetic polymer sets, from 96 to 88 x 10(9)/l (NS) in the heparin-coated sets, and from 93 to 54 x 10(9)/l (p< 0.01) in the uncoated sets after 2 h of recirculation. There were significant differences in platelet counts between the coated sets and the uncoated set at end of experiments (p < 0.05). Beta-thromboglobulin (BTG) concentrations increased in the synthetic polymer sets from 166 to 352 ng/ml (p < 0.01), in the heparin coated sets from 336 to 1168 ng/ml (p < 0.01), and in the uncoated sets from 301 to 3149 ng/ml (p < 0.01) after 2 h of recirculation. The differences in BTG at termination of the experiments were significant among all three sets (p < 0.05). Myeloperoxidase (MPO) concentrations in the synthetic polymer sets increased from 63 to 86 micrograms/l (p < 0.01), in the heparin-coated sets from 90 to 208 micrograms/l (p < 0.01), and in the uncoated sets from 122 to 513 micrograms/l (p < 0.01) after 2 h of recirculation. The differences in MPO at termination of the experiments were significant among all three groups (p < 0.01). There were no significant differences at termination of the experiments among the three sets regarding complement activation as measured by C3 activation products and the terminal complement complex. We conclude that in the current in vitro model of a CPB circuit, the synthetic polymer coating and the heparin coating caused significantly less platelet loss and granulocyte and platelet activation than the uncoated surface (p < 0.05). The synthetic polymer coating caused significantly less granulocyte and platelet activation than the heparin coating (p < 0.05). There was moderate complement activation within each group, but no significant differences among the three groups.

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Section: C3 Complement Activation Productscontrasting

confidence: 50%

Section: Introductionmentioning

confidence: 99%

In vitro evaluation of new surface coatings for extracorporeal circulation

et al. 1999

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“…Several investigators have shown that sulphonated polymers have a characteristic anticoagulant effect and sulphonation is intended to mimic the functional groups responsible for heparin's anticoagulatory effect. 13,14 The present in vitro study was primarily undertaken to evaluate a new CPB surface coating (Avecor) compared to two commercially available coatings in clinical use (CBAS and Duraflo 2).…”

Section: Introductionmentioning

confidence: 99%

Comparison of three oxygenator-coated and one total-circuit-coated extracorporeal devices

et al. 1999

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The present study was designed to compare the biocompatibility of three cardiopulmonary bypass setups with different surface coatings, and to determine if coating of the whole circuit with one of the coatings was more beneficial than coating of the oxygenator only. Extracorporeal devices entirely coated with synthetic polymers (Avecor, n = 6) were compared to oxygenators coated with synthetic polymers (Avecor, n = 6), end-point, covalently attached heparin (CBAS, n = 6) or absorbed heparin (Duraflo 2, n = 6) in an in vitro model of a heart lung machine. The circuits were primed with fresh human whole blood and Ringer's acetate and recirculated at 4 l/min at 30 degrees C for 2 h. Test samples were obtained at regular intervals and analysed for myeloperoxidase (MPO), platelet counts, beta-thromboglobulin, heparin, prothrombin fragment 1+2, plasmin anti-plasmin complexes, and complement activation products. The mean MPO concentrations increased in the Avecor-coated oxygenator group (AV) from 247 at the start to 671 microg/l at the termination of the experiments, in the Avecor-coated total circuit group (AV-T) from 116 to 288 microg/l, in the Duraflo 2 coated oxygenator group (DU) from 160 to 332 microg/l, and in the CBAS-coated oxygenator (CA) group from 172 to 311 microg/l. The MPO concentrations increased significantly in all groups (p < 0.03). The increase in group A was significantly higher than in the other three groups (p = 0.007). The mean platelet counts decreased in the Avecor-coated total circuit group from 117 at start to 99 x 10(9)/l at termination of the experiments, in the Avecor-coated oxygenator group from 119 to 103 x 10(9)/l, in the Duraflo 2 group from 96 to 86 x 10(9)/l, and in the CBAS group from 132 to 123 x 10(9)/l. The platelet counts decreased significantly in all groups (p < 0.01), but the intergroup differences were not significant (p = 0.15). The mean beta-thromboglobulin concentrations increased in the Avecor-coated total circuit group from 193 at the start to 754 ng/ml at the termination of the experiments, in the Avecor-coated oxygenator group from 474 to 1654 ng/l, in the Duraflo 2 group from 496 to 1280 ng/l, and in the CBAS group from 418 to 747 ng/l. The beta-thromboglobulin increase was significant in each group (p < 0.01), but not between the groups (p = 0.49). The mean heparin concentrations in the Duraflo 2 group increased from 2460 at the start to 2897 IU/l at termination of the experiments, in the CBAS group from 2468 to 2518 IU/l. In the Avecor-coated oxygenator group heparin concentrations decreased from 2010 to 1968 IU/l, and in the Avecor-coated total circuit group from 2002 to 1927 IU/l. The differences in heparin concentrations were significant between the Duraflo 2 group and the other groups (p < 0.05). The mean prothrombin fragment 1+2 concentrations increased in the CBAS group from 0.4 at the start to 2.1 nmol/l at the end of the experiments, in the Avecor-coated oxygenator group from 0.4 to 0.6 nmol/l, in the Avecor-coated total circuit group from 0.3 to 0.4 nmol/l,...

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“…This polyelectrolyte (F'LE) was derived from cis-1 ,Cpolyisoprene and contains the following structural units: In an attempt t o improve the blood compatibility of polymeric materials, PLE has been linked to different surfaces either by means of cationic coupling agents (2) or covalently by making use of the residual double bonds in the polyelectrolyte (3). Immobilization of PLE onto polymeric surfaces can also be achieved by reaction of carboxylate groups of PLE with suitable functional groups, present on the polymeric surface.…”

Section: Introductionmentioning

confidence: 99%