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Heparin was covalently immobilized on PSf membranes to obtain a dialysis membrane with high affinity for LDL. WCA and streaming potential measurements were performed to investigate wettability and surface charge of the membranes. The morphology of the membranes was investigated by SEM. An ELISA was used to measure the adsorption and desorption of LDL on plain and modified PSf. Blood compatibility was studied by measurement of thrombin time, partial thromboplastin time, kallikrein activity and platelet adhesion. It was found that the blood compatibility of the membrane was improved by covalent immobilization of heparin at its surface. However, PSf-Hep membrane showed higher flux recovery after BSA solution filtration, which revealed antifouling property of PSf-Hep membranes., (© 2011 WILEY-VCH Verlag GmbH & Co. KGaA, Weinheim.)

The majority of patients with chronic kidney disease are currently treated with dialyzers containing synthetic membranes. Of all the dialysis membranes made from these polymers, 93% are from the parent polyarylsulfone family of which 71% are from polysulfone (PSu) and 22% from polyethersulfone. The preference of nephrologists for PSu dialyzers signifies their versatility in terms of meeting the solute and fluid removal demands for all treatment modalities (low-and high-flux dialysis, online hemodiafiltration, hemofiltration). The unprecedented success and widespread usage of PSu membranes is attributed, in addition to efficient removal of a broad spectrum of uremic toxins, to other criteria required of modern dialysis therapies. Namely, effective endotoxin retention capacity, pronounced intrinsic biocompatibility and low cytotoxicity are factors which all contribute to minimal adverse clinical sequelae. Furthermore, PSu by virtue of its high thermal stability can be sterilized with steam, the preferred mode of sterilization as it does not have the disadvantages associated with other sterilization methods. However, there are significant differences between membranes made from PSu due to differences in membrane polymer recipes and manufacturing technologies. Although PSu may be the main constituent, these membranes are blended with other polymers, e.g. hydrophilizing agents, such as polyvinylpyrrolidone to give each membrane its characteristic profile. The relative amounts of the two (or more) co-polymers as well as the spinning conditions provide a fingerprint of each membrane in terms of solute separation characteristics, biocompatibility, cytotoxicity or endotoxin retention capabilities. PSu membrane-based dialyzers thus fulfill the crucial therapy requirements of current treatment modalities to varying extents. Thereby, different effects towards patient outcomes and treatment safety are achieved., (Copyright © 2011 S. Karger AG, Basel.)

The interaction of blood with artificial surfaces is of particular interest during hemodialysis treatments with extracorporeal blood circuits. Components of the extracorporeal blood circuit are known to have only a moderate, sometimes even an unfavorable hemocompatibility, and thus may provoke adverse biochemical or clinical sequelae. This article describes a newly established hemocompatibility assessment score. This score is based on on a standardized series of in vitro tests and is applied to commercially available hemodialysis membranes. It relates to a variety of membrane polymers, such as regenerated cellulose, diethylaminoethyl-modified cellulose, polyethersulfone/polyarylate blends and polysulfone. In order to compare different polymers used in the manufacturing of dialysis membranes, a set of the following hemocompatibility parameters was assessed and assembled to an overall score: generation of complement factor 5a, thrombin-antithrombin III-complex, release of platelet factor 4, generation and release of elastase from polymorphonuclear granulocytes, and platelet count. With respect to these parameters, the results reveal major differences between the selected dialysis membranes. This new score model proves to be an efficient tool to derive objective results, and it may, thus, be used in the future to facilitate the selection of membrane polymers with an appropriate hemocompatibility pattern for dialysis therapy.

The aim of the study was to assess the biocompatibility profile of a newly developed high-flux polysulfone dialyzer type (FX-class dialyzer). The new class of dialyzers incorporates a number of novel design features (including a new membrane) that have been developed specifically in order to enhance the removal of small- and middle-size molecules. The new FX dialyzer series was compared with the classical routinely used high-flux polysulfone F series of dialyzers. In an open prospective, randomized, crossover clinical study, concentrations of the C5a complement component, and leukocyte count in blood and various thrombogenicity parameters were evaluated before, and at 15 and 60 min of hemodialysis at both dialyzer inlet and outlet in 9 long-term hemodialysis patients using the FX60S dialyzers and, after crossover, the classical F60S, while in another 9 patients, the evaluation was made with the dialyzers used in reverse order. The comparison of dialyzers based on evaluation of the group including all procedures with the FX60S and the group including procedures with the F60S did not reveal significant differences in platelet count, activated partial thromboplastin times, plasma heparin levels, platelet factor-4, D-dimer, C5a, and leukocyte count at any point of the collecting period. Both dialyzer types showed a significant increase in the plasma levels of the thrombin-antithrombin III complexes; however, the measured levels were only slightly elevated compared with the upper end of the normal range. Biocompatibility parameters reflecting the behavior of platelets, fibrinolysis, complement activation, and leukopenia do not differ during dialysis with either the FX60S or the F60S despite their large differences in design and geometry features. Although coagulation activation, as evaluated by one of the parameters used, was slightly higher with the FX60S, it was still within the range seen with other highly biocompatible dialyzers and therefore is not indicative of any appreciable activation of the coagulation system. Thus, the incorporation of various performance-enhancing design features into the new FX class of dialyzers does not result in a deterioration of their biocompatibility profile, which is comparable to that of the classical F series of dialyzers.

The chemical composition of a dialysis membrane is decisive towards determining its physical and biochemical properties--two fundamental determinants of the success of therapy offered to patients suffering from chronic renal failure. From the vast variety of synthetic polymers available, only a few are suitable for the manufacture of dialysis membranes that have to conform to the diverse demands of modern haemodialysis and related therapies. Recently, a membrane labelled as polyamide (Polyamide S) has caused some confusion to end-users in that the product specification for the membrane is given as 'polyarylethersulfone' or simply as Polyamide S membrane. As the chemical and physical properties of these two polymer types are distinctly different, it is unclear whether the functional characteristics of Polyamide S are to be attributed to polyamide, polyarylethersulfone, or, to both polymers. We therefore undertook investigations to ascertain the exact chemical nature of the Polyamide S membrane using a series of chemical analytical tools and an appropriate polyamide reference. The analytical techniques were conventional gel permeation chromatography (GPC), GPC-FTIR coupled spectroscopy using dimethyl acetamide and hexafluoroisopropanol as solvents and nuclear magnetic resonance spectroscopy. Glass transition temperature measurements and quantitative elemental analysis were also carried out. None of the analytical techniques used showed any traces of polyamide in Polyamide S; no aliphatic or aromatic polyamide chemical entities were detected in any of the samples tested. The Polyamide S dialysis membrane thus comprises, solely, of polyarylethersulfone, which is also known as polyethersulfone.

An in vitro set-up has been designed to study the hydraulic permeability of hollow fiber dialysers. Forward and reverse dialysate ultrafiltration were determined using both sterile dialysers and samples with a protein layer settled on the membrane (Fresenius F6, F8, F60 and F80). The ultrafiltration coefficient KUF (ml/h.mmHg) was calculated as the ratio of volumetrical flow (QUF) and transmembrane pressure (TMP) measurements. The protein layer on the membrane was induced either by recirculating human plasma through the dialysers (in vitro) or by a standard hemodialysis session (in vivo). KUF is largely independent of TMP up to 600mmHg (low flux) and 60mmHg (high flux) for forward and reverse flow In sterile dialysers, backfiltration yields a significantly different KUF except for the F80. An in vitro induced protein layer on the membrane decreases KUF15-30% (forward) and 4-12% (backward) in low flux and 45-70% (forward) and 65-73% (backward) in high flux dialysers.

The development of dialysis membranes is closely related to the development of dialysis as a routine therapy for patients with kidney failure. Without having membranes and dialyzers available as commodity products, the treatment of more than 1 million uremic patients worldwide would be impossible. Several transition periods can be identified: a change in membrane geometry from flat sheet to capillaries, a shift in market appreciation from cellulose to synthetic polymers, and from low-flux to high-flux dialyzers. This shift is supported by the notion that convective therapies using high-flux membranes allow the removal of large-molecular-weight solutes. From a historical background, three eras of perception can be identified for both membrane and dialysis development. First, the period of survival when nephrologists had to focus on techniques for blood access and availability of membranes. Second, the period of issues dedicated to rather specific features of membranes and dialysis therapy such as dose of dialysis, reuse, sterilization, and membrane biocompatibility. And third, the period of quality tops this sequence with a complicated approach: the principal area of interest from the medical community has switched to issues such as quality of life, morbidity, mortality, therapy standards, and cost-effectiveness. New membrane developments should focus on this situation.

Renal anemia significantly affects the morbidity and mortality of dialysis patients. The aim of the present study was to establish whether the severity of anemia and success of its treatment differs when using high-flux (HF) or low-flux (LF) hemodialysis. Twenty-five patients on long-term hemodialysis with a mean hematocrit (Hct) of 33%, S alb of 36 g/L, and Kt/V urea of 1.5 were divided into Groups X (n = 13) and Y (n = 12) in a prospective randomized crossover study. Group X was initially treated with LF hemodialysis to be followed by HF hemodialysis for 8 weeks each time. Group Y started with 8 week HF hemodialysis and continued, after crossover, with 8 weeks of LF hemodialysis. HF and LF hemodialysis were performed with polysulfone dialyzers F 7HPS and F60S (Fresenius Medical Care, Bad Homburg, Germany). Hct values, examined at 2 week intervals, did not differ significantly between Groups X and Y during 16 weeks of the study at any measuring interval. In another analysis, all results of HF hemodialysis (first 8 weeks of Y + second 8 weeks of X) were pooled as were all data of LF hemodialysis (first 8 weeks of X + second 8 weeks of Y). No significant relationships were noted between duration of treatment with HF hemodialysis and Hct (n = 72, rS = 0.11, p = 0.36) and between duration of LF hemodialysis and Hct (n = 74, rS = 0.02, p = 0.87) in the newly formed groups. The Hct measured during HF hemodialysis and LF hemodialysis did not differ significantly. Analysis of variance did not reveal a relationship between Hct and the HF or LF membrane. As HF and LF hemodialysis differed significantly in Kt/V urea, the variables were adjusted to identical Kt/V urea using analysis of covariance. No relationship between Hct and dialysis membrane permeability was demonstrated even in this case. Use of biocompatible LF and HF membranes in standard hemodialysis modes under conditions of adequate dose of dialysis and the time period studied did not result in different effects on anemia.

As the quality of water in dialysis fluid varies considerably, dialysate is often contaminated by large amounts of bacteria and endotoxins. Membrane properties and operating pressures are acknowledged to give high-flux dialysis with bicarbonate the bacteriological potential to favor passage of endotoxin fragments from the dialysate into the blood stream. Therefore, a sterile dialysate will have to become a standard. Ultrafiltration across hydrophobic synthetic membranes was shown to remove endotoxins (and their fragments) from dialysis water by the combined effect of filtration and adsorption. However, each module can be used for a limited time only. Ceramic membranes may represent an alternative to polymeric membranes for endotoxin removal. In this article, we tested the capacity of different commercial ceramic membranes with nominal molecular weight cut-off down to 1,000 to retain endotoxins from Ps. aeruginosa. The tested membranes did not generally produce dialysate meeting the Association for the Advancement of Medical Instrumentation standard. When using aluminum-containing membranes, we detected aluminum leaking into the dialysate that could possibly be transported into the blood stream.

Dialysis membranes made from regenerated cellulose are under dispute because of their alleged lack of hemocompatibility. The introduction of membranes from synthetically modified cellulose, like cellulose acetate or Hemophan, has proven, however, that hemocompatible membranes can be fabricated from cellulose by means of chemical surface modifications. In addition to membranes made from modified cellulose like ethers or esters, which were investigated in earlier experiments, we looked for further cellulose modifications to be assessed for their hemocompatibility. For this purpose, we synthesized a series of cellulose carbamate derivatives to profit from the excellent hemocompatibility pattern of the urethane family. In vitro investigations on membranes made from these cellulose modifications proved a direct relationship between the degree of modification and hemocompatibility. This was proven for the following 3 representative hemocompatibility parameters: complement C5a generation, thrombin-antithrombin (TAT) III formation, and platelet count (PC). As already shown for modifications made from cellulose esters, a direct dependency between improved hemocompatibility and the degree of substitution (DS) in the cellulose molecule could be found. In our experiments, a degree of substitution below a value of 0.1 led to a nearly complete suppression of complement activation for all cellulose carbamates under investigation. In contrast to data on cellulose esters, we observed that molecular weight or molecular conformation of chemical substituents exerted only a minor effect on the hemocompatibility pattern. In addition, data on cellulose carbamate esters (e.g., cellulose succinate-phenyl-carbamate) show that a simultaneous but balanced substitution with hydrophilic and hydrophobic groups at the surface of the cellulose polymer is a further prerequisite for optimal hemocompatibility. It seems that the carbamate configuration per se has a positive effect on the hemocompatibility pattern of synthetically modified cellulose membranes.

The development of hemodialysis from an experimental concept to a routine medical therapy is closely related to research, manufacturing and availability of dialysis membranes. Collodion, a cellulose-trinitrate derivative, was the first polymer to be used as an artificial membrane and played a central role in further investigations and applications. Basic studies on the mechanism of solute transport through membranes, like diffusion, were done by A. Fick and T. Graham using collodion as a membrane material. In vivo dialysis in animals and humans was performed with collodion by J. Abel in the USA and G. Haas in Germany. Cellophane and Cuprophan membranes replaced collodion later, because of their better performance and mechanical stability. However, due to its alleged lack of hemocompatibility, membranes made from unmodified cellulose lost their market share. They have been replaced by modified cellulosic and synthetic dialysis membranes which show a better hemocompatibility than unmodified cellulose membranes. Most of the new membrane materials are also available in high-flux modifications and for this reason suitable as well for more effective therapy modes, such as hemodiafiltration and hemofiltration. The success of hemodialysis as a routine therapy is also the success of membrane development, because both, a reproducible membrane production and an unlimited availability of dialysis membranes have increased the number of dialyzed patients to about 1 million patients worldwide in 1999.

Various hollow fibre membranes of polyamide, cellulose and polypropylene were investigated as potential substrata for hepatocyte immobilisation in bioreactors for hybrid liver support systems. Membranes were subjected to a cytocompatibility test in which the attachment and morphology of primary hepatocytes were evaluated. The effect of coating with collagen and fibronectin was also studied. Adequate cell immobilisation was possible on polypropylene and polyamide membranes even without coating. The flattening process of the cells was dependent on the material and the coating. The incorporation of porous polypropylene hollow fibres in hybrid liver cell bioreactors and their specific permeability properties could also offer means for cell oxygenation, metabolite distribution and immuno-isolation purposes.

Numerous articles have been published on the multiple use of dialyzers and on the effect of different reprocessing chemicals and techniques on the dialyzer biocompatibility and performance. The results often appear contradictory, especially those comparing standard biocompatibility parameters. Despite this confusion, a discerning review of the published works allows certain limited conclusions to be drawn. Reprocessing of used hemodialyzers changes the biocompatibility profile of a dialyzer as defined by the parameters complement activation, leukopenia, and cytokine release. The effect of reprocessing depends on the chemicals and reprocessing technique applied and also on the type of membrane polymer being subjected to the reprocessing procedure. Reports of pyrogenic reactions indicate that the flux of the membrane also influences how suitable it is for safe reuse. An increased risk of allergic and pyrogenic reactions appears to be associated with dialyzer reuse. Furthermore, there has been a lack of investigations into the immunologic effect of the layer of adsorbed and chemically altered proteins that remains on the inner surface of reprocessed dialyzers. We conclude that the clinical benefit of dialyzer reuse cannot be generally accepted from a biocompatibility point of view.

Contact phase activation was investigated in vitro using flat sheet type of haemodialysis membranes, Cuprophan (Akzo, Faser, Germany) and AN69S (Hospal, France), and a negatively charged polyamide Ultipor NR 14225 membrane as a control. The investigation focussed on the determination of factor XII-like activity (FXIIA) as an indicator of contact phase activation in the supernatant phase and at the membrane surface after plasma-membrane contact using an incubation test cell. The findings were compared with the observations from a plasma-free system utilizing purified unactivated factor XII. The plasma FXIIA bound to the membrane surface was significantly different between the membranes, while the supernatant phase FXIIA exhibited no significant differences. In contrast, the plasma-free system exhibited significant differences in the supernatant FXIIA and membrane-bound FXIIA for all the materials used and the magnitude of the activity was significantly greater for negatively charged materials. This finding demonstrated the strong influence of the interaction of other plasma constituents on the membrane surface and as such the binding and subsequent activation of factor XII may be altered possibly due to competitive binding and steric hindrance. On the addition of anticoagulants such as heparin, low-molecular-weight heparin, citrate and hirudin, no significant differences were observed in plasma supernatant phase FXIIA. However, each anticoagulant appears to have a distinct influence on the magnitude of plasma membrane-bound FXIIA. On the addition of aprotinin (a kallikrein inhibitor), no significant differences were observed in the plasma supernatant FXIIA. In contrast, aprotinin appears to significantly reduce membrane-bound FXIIA on Cuprophan and polyamide NR, but significantly increase the magnitude of the membrane-bound FXIIA on AN69S.

Haemodialysis membranes with a wide range of solute and hydraulic permeabilities are used clinically. Such membranes are manufactured from either cellulose or synthetic co-polymers and their biocompatibility is commonly characterized by the complement activation and white cell changes observed during their use. The cellobiosic unit may be modified by the partial or total replacement of the hydroxyl groups by diethylaminoethyl (Hemophan), acetate (cellulose acetate), triacetate (cellulose triacetate) or 2,5-acetate (Diaphan). We have undertaken a prospective study in which such renal membranes have been studied in terms of the complement activation and neutropenia produced with the aim of investigating the relationship between modification of the cellobiosic unit and the magnitude of neutropenia and complement activation, and the extent to which membrane base material influences these parameters, by comparing the changes observed in modified cellulose membranes with that for a synthetic membrane (polysulphone). Our findings show that, while the degree of substitution varies between < 1% and total substitution, there is no correlation between the numbers of hydroxyl groups replaced and alteration of complement activation and neutropenia. However, by modification of the cellobiosic unit it is possible to produce a membrane whose biocompatibility is similar to that of a membrane manufactured from a synthetic co-polymer such as polysulphone.

Modern strategies in developing new polymers for dialysis membranes aim to improve their blood compatibility. To achieve such a goal, two approaches have been successfully applied: existing cellulosic polymers were modified, either by introducing functional groups through ester or ether bonds, by mixing synthetic polymers with bulk additives, or by using copolymerization techniques. As a detailed example, the first synthetically modified cellulose membrane, Hemophan, was prepared by substituting some hydrogen atoms in the cellulosic glucose unit by diethyl-amino-ethyl groups with the modification having a considerable impact on the membrane's hemocompatibility. It is further known that the hemocompatibility of hydrophobic synthetic membranes is improved by rendering these materials partially hydrophilic. We tested the hypothesis, whether the hemocompatibility of a material, which is hydrophilic per se, such as unmodified cellulose, is changed after the introduction of hydrophobic substituents. For this purpose, the number and nature of substituents have been systematically varied in order to alter surface properties, and these variations have been subsequently related to blood compatibility parameters. As expected, thrombin generation as well as complement- and cell-activation depend on the number and nature of the substituents whereby some of the substituents show a very narrow optimum if their hemocompatibility is related to the degree of substitution. Changes in hemocompatibility can be followed by physical methods, such as surface angle analyses and zeta potential determinations. Data show that alterations in the lipophilic/hydrophilic balance on the polymer surface may explain substituent-related changes in polymer hemocompatibility.(ABSTRACT TRUNCATED AT 250 WORDS)

Today, more than 30 different polymers or polymer blends are used as materials for dialysis membranes. They can be categorized following the scheme of a family tree of haemodialysis membranes. The trunk represents membranes from regenerated cellulose, major branches show either synthetically modified cellulose membranes or membranes manufactured from synthetic polymers. As the latter are standardly hydrophobic, small branches elucidate the technique on how these materials have been rendered partially or completely hydrophilic. Complications may arise, when comparing membranes only following their polymer names, such as polysulfone, polyacrylonitrile or polyamide. Due to varying polymer compositions, membranes with the same polymer names may differ in their haemocompatibility, flux properties and adsorption characteristics. Adsorption of proteins like beta 2-microglobulin, fibrinogen and coagulation factors, complement proteins, or hormones like parathormon and erythropoietin are differently adsorbed by dialysis membranes and thus adsorption contributes to the removal characteristics. Of central interest for membrane development and application is the question of how these membranes can be sterilized, as a series of patient adverse reactions has been attributed to the dialyser sterilization procedures. Apart from the cellulosic membranes Cuprophan and Hemophan, the majority of membranes cannot be sterilized by steam, as these materials degrade when exposed to above their class-point temperature. Finally, future aspects of modern membrane development should not neglect the needs of patient populations with specific blood properties, such as diabetics.

The majority of dialysis membranes are fabricated from regenerated unmodified cellulose. This standard type of cellulosic membrane is frequently under attack because of its alleged lack of biocompatibility. Recent developments, however, have proven that a chemical modification of the reactive surface groups of regenerated cellulose, the hydroxyl-groups, limits the complement-activating potential of these materials and thus improves its blood-compatibility. We extended the idea of modifying cellulose for improved blood-compatibility to a series of different cellulose esters. Special focus was directed towards the question whether a variation of the type of substituent and degree of substitution could influence the blood-compatibility pattern of these materials: the analysis of blood-compatibility profiles showed a direct dependency on the type of substituent and the degree of substitution (DS). As an example, it was found that the DS, necessary for a complete reduction of complement activation, decreases with increasing chain lengths of aliphatic substituents. Optimal degrees of substitution are characteristic of the type of substituents and enable us to tailor materials specifically for optimized blood compatibility.

In the submitted review the authors give an account of contemporary problems of membranes for dialysis available at present. Although the authors mention also cellulose based membranes (membranes made from unmodified regenerated cellulose, synthetic modified cellulose membranes produced by chemical transformation of cellobiose), the main attention is paid to polymer membranes--typical synthetic polymers, i.e. polysulphone (PSu), polyacrinon nitrate (PAN), polyamide (PA), ethyl vinyl alcohol polymers (EVAL), polyester mixtures formed by polyacrylonitrile and polyether sulphone (PEPA). The authors describe their adsorption capacity, possibility of sterilization and specific problems of interaction with different drugs. In the conclusion the authors outline demands on the development of modern membranes and their problems in future.

Extractable constituents of dialyzer membranes (e.g., monomers and beta-glucans) may induce the production of cytokines in vitro. We therefore studied circulating tumor necrosis factor alpha (TNF alpha) levels in 23 stable hemodialysis patients during treatment with dry Cuprophan membranes (ETO-sterilized n = 10, steam-sterilized n = 13) longitudinally over a period of 4 weeks. After 4 weeks, those 5 patients of each group showing the highest TNF alpha levels were switched to steam-sterilized, wet Cuprophan membranes. No significant increase in plasma TNF alpha was observed during hemodialysis with either ETO- or steam-sterilized dry Cuprophan membranes. A substantial TNF alpha increase (> or = 100% compared to pre-HD values), however, was observed during 14 of 84 treatment sessions. In 5 selected patients with ETO-sterilized, dry Cuprophan dialyzers, TNF alpha rose from (mean +/- SEM) 17.2 +/- 3.0 (pre-HD) to 20.9 +/- 6.2 (120 min) and 21.9 +/- 4.5 pg/ml (240 min). Corresponding levels in patients with steam-sterilized, dry Cuprophan were 16.2 +/- 5.4 (pre-HD), 21.9 +/- 6.8 (120 min), and 16.0 +/- 3.7 pg/ml (240 min), respectively. There was no difference between ETO- and steam-sterilized dialyzers. No significant reduction in mean TNF alpha plasma levels or in frequency of elevated peak levels was achieved when these patients were switched to wet Cuprophan dialyzers for another 4 weeks. It is suggested that an induction of elevated TNF alpha levels during hemodialysis is possible but is not observed regularly during treatment with Cuprophan membranes.(ABSTRACT TRUNCATED AT 250 WORDS)

Basic biocompatibility parameters of dialysis membranes made of non-substituted regenerated cellulose (NRC) and cellulose membranes with hydroxyl groups substituted, to a higher (H) or lower (L) degree, by dl-ethyl-amino-ethyl groups (DEAE), or by acetate (CA) were investigated in a 16-week clinical study, involving 10 long-term haemodialysis patients. In the 15th minute of dialysis, the decrease in blood leukocyte count, while using NRC (0.24 +/- 0.03 of baseline value, arithmetic mean +/- SEM) was deeper compared with that seen in DEAE-L (0.88 +/- 0.10, p < 0.001), in DEAE-H (0.79 +/- 0.10, p < 0.01), and in CA (0.73 +/- 0.05. p < 0.05). In the 15th minute of the procedure, C5a concentrations, reflecting complement activation, were higher in NRC (4.4 +/- 0.51 micrograms/L) than in DEAE-L (1.41 +/- 0.22, p < 0.001), in DEAE-H (1.68 +/- 0.47, p < 0.01), and in CA (1.68 +/- 0.22, p < 0.01). Activated clotting times were, in the 10th minute of the procedure, significantly longer in NRC (2.94 +/- 0.37 of baseline value) than in DEAE-H (1.74 +/- 0.10, p < 0.05) and, by the end of dialysis, the difference between these membranes (NRC: 1.47 +/- 0.21, DEAE-H: 0.85 +/- 0.08, p = 0.07) was close to the level of statistical significance. The authors conclude: 1. Substitution of the hydroxyl groups of regenerated cellulose reduces the decrease in leukocyte count and complement activation in the initial phase of haemodialysis. 2. At the same time, substitution by DEAE groups may raise thrombogenicity, as indicated by the shorter activated clotting times.(ABSTRACT TRUNCATED AT 250 WORDS)

Methods for the detection of positive or negative charges on the surface of biomaterials/membranes and inside a membrane are important for the characterisation of such materials. We tested different dyes and optimized staining procedures. Under standardized conditions negatively charged membranes were stained with cationic triarylmethane compounds such as crystal violet and positively charged membranes with the anionic anthraquinone dye anthralan blue B. There was no staining of uncharged cellulose membranes. The applicability of these methods was demonstrated on membranes coated to varying degrees with charged compounds such as heparin, these changes in charge being detectible quantitatively by photometry. The distribution of charges inside a membrane was detected by optical sectioning across the stained (FITC labelled poly-L-lysine) membrane using confocal laser scanning microscopy (LSM). LSM offers a completely new application possibility in biomaterial and biocompatibility research.

Development of new biocompatible membranes for clinical application needs the expertise of various specialists, chemists, chemical engineers, and clinicians. As the biocompatibility of a membrane cannot be considered in terms of a single biochemical pathway, due to the interrelation between the complement, coagulation, and inflammatory systems, it is difficult to achieve optimal results with one single polymer. A compromise between different approaches has therefore to be found. Membrane development also needs sophisticated test systems, which simulate the clinical situation as closely as possible. Adequate results are achieved with the 'ex vivo' model, which represents open-loop haemodialysis. The ex vivo model gives good results which are close to those from clinical experiments.

An investigation was performed to demonstrate that time-lapse cinematography and computer aided video analysis of cell morphology is suitable to study and compare the characteristics of hepatocytes during the adhesion process to membranes. We chose to compare ordinary cellulose Cuprophan membranes and membranes coated with collagen or fibronectin. Striking differences between uncoated cellulose and fibronectin or collagen coating were seen in the cell count per square millimeter and adhesion behaviour. On the investigated uncoated Cuprophan the hepatocytes were found to attach but not to spread whilst on collagen coated Cuprophan most of the cells spread spherically, and on fibronectin coated membranes most of the cells flattened spherically or polygonally. Time-lapse video microscopy seems to be a valuable technique for assessing the morphologic behaviour of cells in a detailed and quantitative manner in order to improve the hepatocyte culture technique in bioreactors for hybrid systems.

Activation of the complement system during the course of hemodialysis was recognized more than 20 years ago and since then the generation of C3a and C5a desarg has been used as parameters of blood-membrane interaction. More recently, determination of terminal C5b-9 complement complexes has become feasible. In the present study we determined plasma concentrations of C5b-9 complexes during hemodialysis using Cuprophan or Hemophan membranes. As early as 10 min into dialysis, Cuprophan membranes led to higher arterial plasma concentrations of C5b-9 complexes in comparison to Hemophan-containing devices. With Cuprophan, systemic arterial peak values of 237 +/- 27 U/ml were reached 45 min after the onset of dialysis, while corresponding peak values using Hemophan were only 58 +/- 16 U/ml. Venous concentrations of C5b-9 complexes, measured at the outlet of the dialyzer, were 489 +/- 102 U/ml with Cuprophan and 77 +/- 19 U/ml with Hemophan dialyzers. As an index of red cell lysis, plasma levels of free hemoglobin were evaluated. There was hemolysis with both membranes. Free hemoglobin levels increased threefold with Cuprophan and only twofold with Hemophan membranes. Taken together, plasma concentrations of C5b-9 complexes clearly discern between dialysis membranes of high or low compatibility. The fact that there is simultaneous lysis of red cells might indicate that deposition of C5b-9 complexes on innocent cells occurs which would lead subsequently to an array of diverse pathophysiological reactions.

Endotoxins, or fragments thereof, can reach the blood stream of dialysis patients, transported by diffusion and connection across the intact high-flux membrane. This transfer depends upon the phenomenon of back filtration. Back filtration generally occurs under conventional high-flux dialysis conditions with membranes having an ultrafiltration coefficient in blood (UF-C) above 20 ml/hr/m2/mmHg. The clinical consequences of back filtration vary from center to center depending primarily on the quality of dialysate. We therefore surveyed the bacterial and endotoxin levels of purified water and effluent dialysate in a cross section of dialysis centers in the central United States. Using a high recovery medium, we found that 53% of the centers had bacterial counts above the Association for the Advancement of Medical Instruments standard in water (20% cfu/ml) and 35% above the standard in dialysate (2,100 cfu/ml). Endotoxin concentrations higher than 5.0 EU/ml in both water and dialysate were found in 4% and 11.8% of the centers, respectively. Since high-flux membranes are believed to be of benefit for long-term dialysis patients, manufacturers will have to offer dialysate preparation systems with additional safety features. The proper membrane design will be a key to the success of such systems.

One major goal of dialysis therapy has become the removal of beta 2-microglobulin (beta 2-m). The interdialytic elimination of beta 2-m was studied using a newly developed high-flux cellulose acetate (CA) membrane. The results show that high-flux CA dialyzers offer better biocompatibility than classical Cuprophan or high-flux Cuprophan devices, with regard to leukopenia, C3a desarg generation, and elastase release from polymorphonuclear (PMN) leukocytes. Compared to high-flux CA membranes, high-flux PMMA membranes induce less C3a desarg formation but comparable leukopenia. High-flux PMMA membranes, however cause greater leukocyte stimulation than CA as demonstrated by more PMN elastase release during hemodialysis. Using high-flux CA or high-flux PMMA membranes, serum beta 2-m levels decreased 32% during dialysis. Serum beta 2-m dropped 10% with high-flux Cuprophan membranes, but remained unchanged with conventional Cuprophan dialyzers. Sieving coefficients for beta 2-microglobulin (beta 2-m) were virtually zero with classical Cuprophan and 0.66 with high-flux cellulose acetate membranes. High-flux membranes made of Cuprophan and PMMA gave coefficients of 0.25 and 0.45, respectively. This indicates the high removal capacity of the new CA-membrane for substances with high molecular weight. This high-flux CA membrane thus appears to combine a good degree of biocompatibility with a high capacity for beta 2-m removal.

We have previously demonstrated that chemical modification of cellulosic membranes with dimethyl-amino-ethyl (DEAE) groups significantly improves membrane properties in terms of biocompatibility. Here, we show that DEAE substitution also alters the membrane's thrombogenic properties, and cellulosic membranes with various amounts of DEAE substitution were produced. Clinical dialyzers were constructed using two experimental membrane materials: modified cellulose-low (MC-low) and MC-high; standard unsubstituted cellulose was used as a control. Six patients were treated for a period of 3 weeks with each type of dialyzer and a heparin dose of less than 6000 IU/treatment. MC-low exhibited less extracorporeal beta-thromboglobulin and thromboxane B2 release than MC-high or Cuprophan. In addition, residual blood volume after clinical use was lower in the MC-low type. MC-low and MC-high induced less complement activation than Cuprophan, as characterized by extracorporeal C5a and C3a plasma concentrations (75% less C5a generation and 50 to 70% less C3a generation than unsubstituted cellulose).

Of the two main classes of dialysis membranes, cellulosic and synthetic, the former represents the standard membrane used in dialysis therapy. The disputed properties of cellulosic membranes related to biocompatibility have inspired a number of authors to compare these two membrane classes from a variety of perspectives. However, such a strict categorization as "synthetic" or "cellulosic" is of doubtful value from the point of view of polymer chemistry. Here, biocompatibility and performance properties of these two membrane classes are compared with the aim of investigating the validity of this categorization. The biocompatibility parameters studied are complement and leukocyte activation together with activation of the coagulation cascade. Analysis of a variety of both cellulosic and synthetic membranes with different degrees of biocompatibility showed that biocompatibility can be achieved by both classes of membranes and is, therefore, not a particular property of one class only. Furthermore, performance and beta 2-microglobulin removal properties of the two classes of membranes do not particularly favor one of these classes. Therefore, differences between cellulosic and synthetic membranes are not manifested in parameters like biocompatibility, hydraulic permeability, and overall performance.