Plasmapheresis membrane and process for the preparation thereof

Plasmapheresis membranes of hydrophilic polycarbonates are disclosed, comprising polycondensates of bisphenol A and a polyalkylene oxide. These membranes which have a regular pore structure with smoothly rounded pores with openings without sharp edges, have an average pore diameter of about 0.01 to 0.8.mu., a porosity preferably above 65%, and a thickness of between about 50 and 300.mu.. Processes for preparing these membranes are also disclosed, including casting a 3 to 20 weight percent polycarbonate polymer solution onto a smooth surface, contacting the layer with a gelling medium prior to precipitation of the membrane, and subsequent precipitation of the gelled layer to form the membrane.

FIELD OF THE INVENTION 
The present invention relates to a microporous membrane of biocompatible 
polymer for use in plasmapheresis. 
More particularly, the present invention relates to a process for the 
preparation of such a membrane, wherein a solution of the biocompatible 
polymer is applied in the form of a layer upon a smooth surface and, 
thereafter, is precipitated and washed so as to form said membrane. 
BACKGROUND OF THE INVENTION 
The expression "plasmapheresis" is intended to mean a blood separation 
procedure in which blood cells are separated from plasma by means of a 
membrane which is permeable to the plasma but which retains, i.e., is not 
permeable, to the blood cells. Such a procedure differs from other similar 
types of blood separation procedures, such as hemofiltration, with respect 
to the cut-off point with regard to the passage of molecules for the 
specific membrane which is utilized therein. In hemofiltration, for 
example, that cut-off point is usually of the order of magnitude of 
10.sup.3 -5.times.10.sup.4 Dalton, while the corresponding cut-off point 
in connection with plasmapheresis is about 3.times.10.sup.6 Dalton. 
In the literature various membranes (as well as processes for their 
preparation) are described which are of the above-mentioned kind. For 
example, in Trans. Am. Soc. Artif. Inter. Org. 1978, pp. 21-26 the use of 
a hydrophobic polycarbonate membrane having pores which are formed through 
neutron radiation and etching in association therewith is described. This 
membrane displays a regular pore structure, but has a low porosity. 
Furthermore, the pore openings comprise a sharp edge which may cause the 
destruction of blood cells (hemolysis), when such membranes are used in 
plasmapheresis. Furthermore, due to its low porosity as well as the 
polymeric characteristics thereof, said membrane also has a low filtration 
capacity, such as about 0.004 ml/sec. x at x cm.sup.2. 
In the above-noted article, as well as in DE-OS 22 57 697 and DE-OS 28 28 
616, plasmapheresis membranes which are prepared from cellulose acetate 
are described, both in the form of hollow fibers and in the form of flat 
sheets. Again, however, there is also a risk of hemolysis with these 
membranes. A further disadvantage in connection with these prior membranes 
is the fact that they have a low permeability for substances having 
molecular weights of between 1.times.10.sup.6 and 3.times.10.sup.6 Dalton. 
For example, the permeability coefficient for factor VIII (having a 
molecular weight of 2.times.10.sup.6) is as low as 0.2-0.4. Furthermore, 
the Nieviny coefficient for high molecular weight substances (above about 
500,000 Dalton) drastically decreases after filtrations for about 15 to 30 
minutes. 
In British Pat. No. 1,556,898 a polycarbonate membrane is described for use 
in hemodialysis. These hemodialysis membranes are prepared from polymers 
having recurring units of the formula 
##STR1## 
in which A can be --CH.sub.2 CH.sub.2 O-- or --CH.sub.2 CH.sub.2 O-- 
and/or --C.sub.3 H.sub.6 O--, etc. The membranes discussed in this patent 
are useful in connection with hemodialysis, and thus by definition must 
have pore sizes which are quite small and which can only pass molecular 
sizes of up to about 20,000 Dalton. Specifically, they have pore sizes of 
up to about 0.008.mu. (about 80 .ANG.), i.e., between about 0.002 and 
0.008.mu.. Furthermore, these membranes have hydraulic permeabilities 
generally of between about 2 and 6 ml/hr/m.sup.2 /mmHg. Furthermore, the 
membranes set forth in this patent are prepared by a wet phase inversion 
technique employing an aqueous gelation system with water as the gelling 
medium and a water-miscible organic solvent as the casting solvent. These 
polycarbonate membranes are thus prepared by casting a layer of the 
polyether-polycarbonate block copolymer onto a smooth substrate surface 
with a water-miscible organic solvent, together with a co-solvent which 
acts as a swelling agent for the copolymer, then drying that layer to 
partially evaporate the solvents and immersing the partially dried layer 
in water to form a gelled membrane which can then be stripped from the 
substrate surface. The preferred solvents used therein are 1,3-Dioxolane, 
1,3-Dioxan, 1,4-Dioxan, dimethyl formamide, pyridine, and several others. 
The additional swelling agents can include dimethyl formamide, dimethyl 
acetamide, acetamide, formamide, pyridine, etc. 
In the procedure set forth in patents such as the above-noted British 
patent, the evaporation step is important to partially remove the solvent 
and form a dense membrane structure. The membrane can then be immersed in 
the water bath to both gell and precipitate same, and during this entire 
procedure the solvent is completely removed from the membrane. 
Furthermore, in a recent patent application, Ser. No. 257,929, filed on 
Apr. 23, 1981 assigned to Gambro Inc., modified polycarbonate membranes 
are disclosed for use in hemofiltration processes. These membranes are 
similar to those set forth above, but are produced by a process which 
permits the membrane to be used in hemofiltration processes, and have 
ultrafiltration rates of at least about 7 ml/hr/m.sup.2 /mmHg. These 
membranes, like those of the aforementioned British patent, have pore 
sizes of up to about 0.008.mu., i.e. between about 0.002 and 0.008.mu.. In 
the procedure disclosed in this co-pending application, the layer of 
polyether-polycarbonate block copolymer and water-miscible organic solvent 
are again dried by partial evaporation of the solvent subsequent to 
casting, and prior to immersion in water to gell the membrane. In one 
embodiment of that invention, an aqueous solution of an oxidizing agent is 
contacted with the membrane either subsequent to gelation or as part of 
the gelation process itself, while in yet another embodiment subsequent to 
gelation and precipitation of the membrane the gelled membranes are 
treated with swelling agents, such as glycerine or other polyols or 
polyethylene glycols, and/or mixtures of these compounds with various 
alcohols. 
One of the objects of the present invention is therefore to provide a 
microporous membrane of a biocompatible polymer comprising a hydrophilic 
polycarbonate for use in plasmapheresis, which in contrast to the 
above-noted prior art membranes displays a regular pore structure 
comprising smoothly rounded pore openings without sharp edges. 
Furthermore, it is another object of this invention to provide such 
membranes having a high permeability or filtration capacity for high 
molecular substances of up to 3.times.10.sup.6 Dalton, to therefore also 
provide a high filtration rate for plasma, without drastically decreasing 
permeability coefficients. 
A further object of this invention is to provide a process for the 
preparation of such an improved membrane for plasmapheresis. 
SUMMARY OF THE INVENTION 
These and other objects have now been achieved by the discovery of a 
microporous membrane of a biocompatible polymer. Said membrane is 
characterized in that said polymer is a hydrophilic polycarbonate. 
In particular, the plasmapheresis membranes according to the present 
invention are microporous hydrophilic polycarbonate polymers comprising a 
polycondensate of bisphenol A and polyalkylene oxide having an average 
pore diameter of between about 0.01 and 0.8.mu. whereby the membrane is 
permeable by molecules of about 50,000 Dalton, and up to about 
3.times.10.sup.6 Dalton. In particular, in a preferred embodiment the 
pores of the membrane are smoothly rounded and substantially free of sharp 
edges whereby hemolysis is substantially avoided when these membranes are 
employed for plasmapheresis. In particular, it is preferred that these 
membranes have an average pore diameter of about 0.6.mu., and preferably 
have a porosity above about 65%, and a thickness of between about 50 and 
300.mu.. 
In accordance with the process of the present invention, plasmapheresis 
membranes are prepared by initially preparing a solution of from about 3 
to 20 weight percent of a biocompatible, polycarbonate polymer, comprising 
a polycarbonate bisphenol A and polyalkylene oxide, applying a layer of 
that solution to a smooth surface, contacting the layer of solution with a 
gelling medium prior to precipitation of the membrane from the 
biocompatible polymer, thereafter precipitating the gelled layer of the 
solution so as to form the membrane therefrom, and washing the membrane. 
In accordance with another embodiment of the process of the present 
invention, the contacting of the layer of the solution of biocompatible 
polymer with the gelling agent is conducted without any intermediate 
drying of that layer subsequent to its application to the smooth surface. 
In accordance with another embodiment of the process of the present 
invention the solution of biocompatible polymer includes two solution 
components, an aromatic solvent component for the polymer and a 
non-solvent component for the polymer. Preferably, the solvent for the 
polymer can include compounds such as dioxane, dioxylane, dimethyl 
sulfoxide, dimethyl formamide, etc. Furthermore, the non-solvent for the 
polymer can include compounds such as polyalkylene oxides, salts, 
glycerine, polyvinyl pyrrolidone, etc. 
In accordance with another embodiment of the process of the present 
invention, the gelling medium employed includes a pair of gelling medium 
components, the first being a polar solvent for the polymer and the second 
being an alcohol. In a preferred embodiment, the polar solvent comprises 
dimethyl formamide and the alcohol used will be methanol. 
In accordance with another embodiment of the process of the present 
invention, the membrane is post-treated after it is precipitated by 
subsequent contact with an alcohol, followed by contact with a mixture of 
an alcohol with glycerine. In a preferred embodiment after this two stage 
contacting the alcohol is evaporated at reduced temperatures so that the 
glycerine is not removed from the membrane and the membrane is therefore 
made shelf stable by the presence of the glycerine therein. 
DETAILED DESCRIPTION 
Examples of hydrophilic polycarbonates which can be used in accordance with 
the present invention are polycondensates of bisphenol A and polyalkylene 
oxide. For example, said polycondensates may be represented by the 
following general chemical formula: 
##STR2## 
where R is --CH.sub.2 CH.sub.2 -- or combinations of --CH.sub.2 --CH.sub.2 
--CH.sub.2 -- and --CH.sub.2 --CH.sub.2 --, but preferably --CH.sub.2 
CH.sub.2, and where m is from about 40 to 100, preferably about 80, n is 
from about 10 to 155, preferably about 152, and p is from about 0.5 to 3, 
preferably about 1. 
Preferably, the polycondensate is the polycondensation product of bisphenol 
A and a polyalkylene oxide having a molecular weight of from about 600 to 
20,000 Dalton. Said polyalkylene oxide is thereby used in amounts ranging 
from about 5 to 40, preferably about 35. 
Conveniently, the present membrane has an average pore diameter of from 
about 0.01 to 8.mu., preferably 0.1 to 0.8.mu., and more preferably about 
0.6.mu.. Furthermore, its porosity is usually about 65%, so as to insure 
high filtration rates. 
The membrane thickness may vary as desired, but is generally from about 50 
to 300.mu.. Preferably, the thickness of the membrane is about 100.mu.. 
In the present process a hydrophilic polycarbonate, preferably having the 
above chemical formula, is employed as the biocompatible polymer. 
The polymer solution preferably includes an aromatic solvent, or mixtures 
of such solvents, and a non-solvent, and the hydrophilic polycarbonate is 
generally present in amounts ranging between about 3 and 20% by weight, 
preferably between about 3 and 15% by weight, and most preferably between 
about 3 and 10% by weight. The non-solvent is used in amounts of up to 
about 15%, such as between about 1 and 6%. 
Examples of the aromatic solvents which may be used are dioxane, dioxolane, 
dimethyl sulfoxide (DMSO), dimiethyl formamide (DMF), and mixtures 
thereof. Examples of the non-solvents which may be used are the 
polyalkylene oxides, a salt, glycerine, polyvinyl pyrrolidone (PVP), etc. 
The viscosity of the polymer solution is usually between about 200 and 
20,000 cP, and preferably about 700 cP, measured at 20.degree. C. 
The polymer solution is preferably applied to the smooth surface by casting 
same with a casting gap having a height which is pre-set to a suitable 
value which depends upon the desired final membrane thickness. Preferably, 
dust-free conditions, with nitrogen, are utilized for application of the 
polymer solution, and this is done at a constant temperature, such as from 
about 10.degree. to 25.degree. C. 
Alternatively, the polymer solution may be extruded in the form of a hollow 
fiber by using special center-liquids which are simultaneously extruded 
through the center cavity of the die which is utilized. 
In accordance with one aspect of the present invention, a mixture of a 
polar solvent and an alcohol is used as the gelling medium. For example, 
DMF may be used as the polar solvent, and methanol may be used as the 
alcohol. The mixing ratio between the DMF and methanol may vary between 
about 2:1 and 1:2, and preferably will be about 1:1. 
The temperature of the gelling medium is generally suitably maintained at 
from about 15.degree. to 25.degree. C., most preferably about 21.degree. 
C. 
In order for the finished membrane to exhibit shelf-stable characteristics, 
the membrane can be exposed to a post-treatment. Such post-treatment can 
comprise sequential treatments with alcohols and an alcohol/glycerine 
mixture. The alcohol is then removed from the membrane so as to leave 
glycerine, making the membrane shelf-stable. Conveniently, the alcohol is 
removed through evaporation at low temperatures, such as temperatures 
between 40.degree. and 70.degree. C. 
The membranes which are prepared according to this process are symmetrical 
and self-supporting, and have a thickness of between about 50 and 300.mu., 
preferably of about 100.mu.. Furthermore, they display high flexibility. 
A special characteristic of these membranes is their ability to be welded, 
i.e., utilizing welding temperatures of between about 180.degree. and 
200.degree. C. 
In order to measure the filtration capacity of these membranes as used for 
plasmapheresis a special plasmapheresis cell is employed having defined 
flow rates, with a membrane surface of 45 cm.sup.2, a transmembrane 
pressure of 100 mmHg, and a blood flow of 100 ml/minute at 20.degree. C., 
in the following manner. 
Blood having a hematocrit of 25% and a total protein concentration of 70 
gram/liter was employed. The measured value, i.e., the permeate per time, 
pressure and surface was 10 ml/minute. The retaining capacity for, for 
Example 1, factor VIII (molecular weight 2.times.10.sup.6) was about 5% 
under these conditions.

The present invention is further illustrated by the following examples. 
EXAMPLE 1 
Seven percent of a polycarbonate obtained through polycondensation between 
bisphenol A and polyethylene glycol (PEG) 5000 (in a ratio of 6.5:3.5), 
was dissolved in 90% 1,3-dioxalane at room temperature, mixed with 3% PEG 
10000, filtered through a 2.mu. filter, and degassed under vacuum. The 
solvent viscosity was 1000 cP at 20.degree. C. The polymer solution, as 
case on a smooth surface, was transported through a methanol/DMF-bath (at 
a ratio of 1:1) at 20.degree. C., and residence times of at least 1 minute 
were used. While still on that surface, the gelled polymer layer was 
transported sequentially through wash baths with water at 20.degree., 
40.degree. and 60.degree. C. The membrane was then removed from the smooth 
surface. 
The membrane prepared according to this example had the following 
characteristics: 
Filtration for water (20.degree. C., 0.1 bar): 3 ml/sec. x at x cm.sup.2 
Retention capability for factor VIII: 5% 
Permeability to albumin 68000: 100% 
Retention capability for total protein: 0% 
EXAMPLE 2 
Six percent polycarbonate was dissolved in 90% 1,3-dioxalane at room 
temperature, mixed with 4% pluriol 6800 (polypropylene-polyethylene oxide 
block polymer), filtered and degassed. The solution was cast on a belt, 
transported through a DMSO/methanol-bath (at a ratio of 1:1), and 
thereafter through a water bath at 20.degree. C. 
The membrane prepared according to this example had the following 
characteristics: 
Filtration for water (0.1 bar): 0.1 ml/sec. x at x cm.sup.2 
Retention capability for factor VIII: 30% 
Permeability to albumin 68000: 100% 
Retention capability for total protein: 20% 
EXAMPLE 3 
Seven percent of the polycarbonate obtained through polycondensation 
between bisphenol A and PEG 5000 (at a ratio of 6.5:3.5), was dissolved in 
90% 1,3-dioxalane at room temperature, mixed with 3% PEG 10000, filtered 
over a 2.mu. filter and degassed under vacuum. The solvent viscosity was 
1000 cP at 20.degree. C. The solution, as case on a belt, was then 
transported through a DMSO/methanol-bath (at a ratio of 2:1), and the 
residence time in the bath was at least 2 minutes. The so cast and gelled 
polymer layer was then transported through a water bath at 25.degree. C. 
The membrane prepared according to this example had the following 
characteristics: 
Filtration for water (0.1 bar): 0.1 ml x sec. x at x cm.sup.2 
Retention capability for factor VIII: 80% 
Permeability to albumin 68000: 70% 
Retention capability for total protein: 30% 
The present membrane is intended for use in plasmapheresis, i.e., a blood 
separation procedure in which whole blood is separated into blood cells 
and plasma by contacting the whole blood with one side of these membranes, 
wherein the blood cells and plasma by contacting the whole blood with one 
side of these membranes, wherein the blood cells are retained on that one 
side while the plasma penetrates through the membrane and is collected on 
the other side thereof. This separation is conducted, under the influence 
of a pressure gradient which is maintained between the two sides of the 
membrane. 
It will be understood that the embodiment described herein is merely 
exemplary and that a person skilled in the art may make many variations 
and modifications without departing from the spirit and scope of the 
invention. All such modifications and variations are intended to be 
included within the scope of the invention as defined in the appended 
claims.