CA2238648C - Hydrophilic, swellable coatings for biosensors - Google Patents
Hydrophilic, swellable coatings for biosensors Download PDFInfo
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- CA2238648C CA2238648C CA002238648A CA2238648A CA2238648C CA 2238648 C CA2238648 C CA 2238648C CA 002238648 A CA002238648 A CA 002238648A CA 2238648 A CA2238648 A CA 2238648A CA 2238648 C CA2238648 C CA 2238648C
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/1486—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using enzyme electrodes, e.g. with immobilised oxidase
- A61B5/14865—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using enzyme electrodes, e.g. with immobilised oxidase invasive, e.g. introduced into the body by a catheter or needle or using implanted sensors
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/41—Detecting, measuring or recording for evaluating the immune or lymphatic systems
- A61B5/411—Detecting or monitoring allergy or intolerance reactions to an allergenic agent or substance
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08G—MACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
- C08G18/00—Polymeric products of isocyanates or isothiocyanates
- C08G18/06—Polymeric products of isocyanates or isothiocyanates with compounds having active hydrogen
- C08G18/28—Polymeric products of isocyanates or isothiocyanates with compounds having active hydrogen characterised by the compounds used containing active hydrogen
- C08G18/40—High-molecular-weight compounds
- C08G18/48—Polyethers
- C08G18/4833—Polyethers containing oxyethylene units
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- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08G—MACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
- C08G18/00—Polymeric products of isocyanates or isothiocyanates
- C08G18/06—Polymeric products of isocyanates or isothiocyanates with compounds having active hydrogen
- C08G18/28—Polymeric products of isocyanates or isothiocyanates with compounds having active hydrogen characterised by the compounds used containing active hydrogen
- C08G18/40—High-molecular-weight compounds
- C08G18/61—Polysiloxanes
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- C08G—MACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
- C08G18/00—Polymeric products of isocyanates or isothiocyanates
- C08G18/06—Polymeric products of isocyanates or isothiocyanates with compounds having active hydrogen
- C08G18/28—Polymeric products of isocyanates or isothiocyanates with compounds having active hydrogen characterised by the compounds used containing active hydrogen
- C08G18/65—Low-molecular-weight compounds having active hydrogen with high-molecular-weight compounds having active hydrogen
- C08G18/66—Compounds of groups C08G18/42, C08G18/48, or C08G18/52
- C08G18/6666—Compounds of group C08G18/48 or C08G18/52
- C08G18/667—Compounds of group C08G18/48 or C08G18/52 with compounds of group C08G18/32 or polyamines of C08G18/38
- C08G18/6674—Compounds of group C08G18/48 or C08G18/52 with compounds of group C08G18/32 or polyamines of C08G18/38 with compounds of group C08G18/3203
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- C08G—MACROMOLECULAR COMPOUNDS OBTAINED OTHERWISE THAN BY REACTIONS ONLY INVOLVING UNSATURATED CARBON-TO-CARBON BONDS
- C08G77/00—Macromolecular compounds obtained by reactions forming a linkage containing silicon with or without sulfur, nitrogen, oxygen or carbon in the main chain of the macromolecule
- C08G77/42—Block-or graft-polymers containing polysiloxane sequences
- C08G77/458—Block-or graft-polymers containing polysiloxane sequences containing polyurethane sequences
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- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08J—WORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
- C08J5/00—Manufacture of articles or shaped materials containing macromolecular substances
- C08J5/20—Manufacture of shaped structures of ion-exchange resins
- C08J5/22—Films, membranes or diaphragms
- C08J5/2287—After-treatment
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- C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
- C12Q—MEASURING OR TESTING PROCESSES INVOLVING ENZYMES, NUCLEIC ACIDS OR MICROORGANISMS; COMPOSITIONS OR TEST PAPERS THEREFOR; PROCESSES OF PREPARING SUCH COMPOSITIONS; CONDITION-RESPONSIVE CONTROL IN MICROBIOLOGICAL OR ENZYMOLOGICAL PROCESSES
- C12Q1/00—Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions
- C12Q1/001—Enzyme electrodes
- C12Q1/002—Electrode membranes
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- C—CHEMISTRY; METALLURGY
- C12—BIOCHEMISTRY; BEER; SPIRITS; WINE; VINEGAR; MICROBIOLOGY; ENZYMOLOGY; MUTATION OR GENETIC ENGINEERING
- C12Q—MEASURING OR TESTING PROCESSES INVOLVING ENZYMES, NUCLEIC ACIDS OR MICROORGANISMS; COMPOSITIONS OR TEST PAPERS THEREFOR; PROCESSES OF PREPARING SUCH COMPOSITIONS; CONDITION-RESPONSIVE CONTROL IN MICROBIOLOGICAL OR ENZYMOLOGICAL PROCESSES
- C12Q1/00—Measuring or testing processes involving enzymes, nucleic acids or microorganisms; Compositions therefor; Processes of preparing such compositions
- C12Q1/001—Enzyme electrodes
- C12Q1/005—Enzyme electrodes involving specific analytes or enzymes
- C12Q1/006—Enzyme electrodes involving specific analytes or enzymes for glucose
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
- A61B5/14532—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
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- C—CHEMISTRY; METALLURGY
- C08—ORGANIC MACROMOLECULAR COMPOUNDS; THEIR PREPARATION OR CHEMICAL WORKING-UP; COMPOSITIONS BASED THEREON
- C08J—WORKING-UP; GENERAL PROCESSES OF COMPOUNDING; AFTER-TREATMENT NOT COVERED BY SUBCLASSES C08B, C08C, C08F, C08G or C08H
- C08J2323/00—Characterised by the use of homopolymers or copolymers of unsaturated aliphatic hydrocarbons having only one carbon-to-carbon double bond; Derivatives of such polymers
- C08J2323/02—Characterised by the use of homopolymers or copolymers of unsaturated aliphatic hydrocarbons having only one carbon-to-carbon double bond; Derivatives of such polymers not modified by chemical after treatment
- C08J2323/04—Homopolymers or copolymers of ethene
- C08J2323/06—Polyethene
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- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10T—TECHNICAL SUBJECTS COVERED BY FORMER US CLASSIFICATION
- Y10T428/00—Stock material or miscellaneous articles
- Y10T428/31504—Composite [nonstructural laminate]
- Y10T428/31551—Of polyamidoester [polyurethane, polyisocyanate, polycarbamate, etc.]
Abstract
Methods for reducing the electrode impedance of implantable biosensors by coating the surface of the biosensor with a uniform hydrogel which allows unimpeded water movement around the sensor are provided.
The surface coatings are compositions which are biocompatible and are capable of water uptake of at least 120 % of their weight, more preferably at least 200 % of their weight. Upon the uptake of water, the hydrogels used in the present invention will also swell and provide a layer of water around the electrodes to which the hydrogels are attached. The hydrogels can be prepared from (a) a diisocyanate, (b) a hydrophilic polymer which is a hydrophilic diol, a hydrophilic diamine, or a combination thereof, and optionally, (c) a chain extender.
The surface coatings are compositions which are biocompatible and are capable of water uptake of at least 120 % of their weight, more preferably at least 200 % of their weight. Upon the uptake of water, the hydrogels used in the present invention will also swell and provide a layer of water around the electrodes to which the hydrogels are attached. The hydrogels can be prepared from (a) a diisocyanate, (b) a hydrophilic polymer which is a hydrophilic diol, a hydrophilic diamine, or a combination thereof, and optionally, (c) a chain extender.
Description
HYDROPHILIC, SWELLABLE COATINGS FOR BIOSENSORS
FIELD OF THE INVENTION
This invention lies in the field of polymer chemistry in which the polymers formed are suitable for coating biosensors. The coatings act to decrease the impedance at the sensor's electrode and thereby enhance the signal during in vivo placement of the sensor.
BACKGROUND OF THE INVENTION
Biosensors are small devices that use biological recognition properties for selective analysis of various analytes or biomolecules. Typically, the sensor will produce a signal that is quantitatively related to the concentration of the analyte.
To achieve a quantitative signal, a recognition molecule or combination of molecules is often immobilized at a suitable transducer which converts the biological recognition event into a quantitative response.
A variety of biosensors have been developed for use with numerous analytes. Electroenzymatic biosensors use enzymes to convert a concentration of analyte to an electrical signal. Immunological biosensors rely on molecular recognition of an analyte by, for example, antibodies. Chemoreceptor biosensors use chemoreceptor arrays such as those of the olfactory system or nerve fibers from the antennules of the blue crab WO 98117995 PCTlUS97/19513 2 _ Callinectes sapidus to detect the presence of amino acids in concentrations as low as 10-9 M. For a review of some of the operating principles of biosensors, see Bergveld, et al., ADVANCES fN BIOSENSORS, Supplement I, p. 3I-91, Turner ed., and Collison, et al., ' __ Anal. Chem. 62:425-437 (1990).
S Regardless of the type of biosensor, each must possess certain properties to function in vivo and provide an adequate signal. First, the elements of the biosensor must - be compatible with the tissue to which it is attached and be adequately shielded from adjacent tissues such that allergic or toxic effects are not exerted. Further, the sensor should be shielded from the environment to control drift in the generated signal. Finally, , the sensor should accurately measure the analyte in the presence of proteins, electrolytes and medications which may interfere.
One of the problems with implantable biosensors occurs as a result of "road block" type interference. This problem is encountered when the outermost layer of the biosensor has some hydrophobic characteristics. These characteristics result in the accumulation of plasma proteins on the surface of the electrode after only short periods of direct contact with body fluids. The hydrophobic regions of the sensor surface are believed to denature the proteins resulting in large deposits of protein mass.
The deposits then affect the sensor's performance through a physical interference in a "road block"
type of effect. The protein deposition is a gradual process which creates a non-uniform, non-predictable diffusion path for the analyte to the sensor. Moreover, the effect on the sensor is a cascading type in which the protein deposits dissapate the normal voltages _ applied to the electrodes (i.e., the deposits increase the capacitance of the system). The resultant requirement for higher voltages to offset the increased capacitance increases the noise, ultimately compromising the validity of the sensor's output.
Other problems are also associated with implantable sensors having hydrophobic regions at the sensor's surface. do particular, subcutaneous tissue contains - substantial amounts of lipid vesicles. By implanting a biosensor directly into tissue, a portion of the sensor may be implanted directly into, or flush against a very hydrophobic lipid region. This also limits the aqueous environment which is required around the sensor's electrodes.
What is needed in the art are new coatings for implantable sensors which are extremely hydrophilic and provide a substantial and uniform aqueous flow around the sensors. Quite surprisingly, the present invention provides such coatings and sensors equipped with those coatings.
SUMMARY OF THE INVENTION
The present invention provides methods for reducing the electrode impedance of implantable biosensors by coating the surface of the biosensor with a uniform hydrogel which allows unimpeded water movement around the sensor. The surface coatings are compositions which are biocompatible and are capable of water uptake of at least 120% of their weight, more preferably at least 200% of their weight. Upon the uptake of water, the hydrogels used in the present invention will also swell and provide a layer of water around the electrodes to which the hydrogels are attached.
In one group of embodiments, the hydrogels can be prepared from:
(a) a diisocyanate, (b) a hydrophilic polymer which is a hydrophilic diol, a hydrophilic diamine, or a combination thereof, and optionally, (c) a chain extender.
In one embodiment, there is provided a method of reducing electrode impedance of an implantable biosensor comprising coating the biosensor with a hydrogel, wherein the hydrogel is formed from a reaction mixture of (a) a diisocyanate, the diisocyanate comprising about 50 mol% of the reactants in said mixture; (b) a hydrophilic polymer which is a member selected from the group consisting of a hydrophilic polymer diol, a hydrophilic polymer diamine and combinations thereof; and optionally; (c) a chain extender, the hydrogel having a water pickup of from about 120% to about 400%
by weight.
In another embodiment, there is provided an implantable biosensor having a hydrogel coating, the coating prepared from a reaction mixture of: (a) a diisocyanate, the diisocyanate comprising about 50 mol% of the reactants in the mixture; (b) a hydrophilic polymer which is a member selected from the group consisting of a hydrophilic polymer diol, a hydrophilic polymer diamine and combinations thereof; and optionally;
(c) a chain extender; wherein the coating has a water pickup of from about 120% to about 400% by weight.
3a The present invention further provides implantable biosensors for measuring a variety of analytes, the biosensor having a coating as described above.
BRIEF DESCRIPTION OF THE DRAWINGS
Figure 1 illustrates polymerization reactions of a diisocyanate with a poly(alkylene) glycol or a diamino poly(alkylene oxide) which results in a polyurethane or polyurea, respectively.
Figures 2 and 3 provide the structure of certain aliphatic and aromatic diisocyanates which are useful in forming the coatings described below.
Figure 4 provides the structures of a number of hydrophilic polymers including poly(alkylene) glycols and diamino poly(alkylene oxides) which are used in polymers described below.
FIELD OF THE INVENTION
This invention lies in the field of polymer chemistry in which the polymers formed are suitable for coating biosensors. The coatings act to decrease the impedance at the sensor's electrode and thereby enhance the signal during in vivo placement of the sensor.
BACKGROUND OF THE INVENTION
Biosensors are small devices that use biological recognition properties for selective analysis of various analytes or biomolecules. Typically, the sensor will produce a signal that is quantitatively related to the concentration of the analyte.
To achieve a quantitative signal, a recognition molecule or combination of molecules is often immobilized at a suitable transducer which converts the biological recognition event into a quantitative response.
A variety of biosensors have been developed for use with numerous analytes. Electroenzymatic biosensors use enzymes to convert a concentration of analyte to an electrical signal. Immunological biosensors rely on molecular recognition of an analyte by, for example, antibodies. Chemoreceptor biosensors use chemoreceptor arrays such as those of the olfactory system or nerve fibers from the antennules of the blue crab WO 98117995 PCTlUS97/19513 2 _ Callinectes sapidus to detect the presence of amino acids in concentrations as low as 10-9 M. For a review of some of the operating principles of biosensors, see Bergveld, et al., ADVANCES fN BIOSENSORS, Supplement I, p. 3I-91, Turner ed., and Collison, et al., ' __ Anal. Chem. 62:425-437 (1990).
S Regardless of the type of biosensor, each must possess certain properties to function in vivo and provide an adequate signal. First, the elements of the biosensor must - be compatible with the tissue to which it is attached and be adequately shielded from adjacent tissues such that allergic or toxic effects are not exerted. Further, the sensor should be shielded from the environment to control drift in the generated signal. Finally, , the sensor should accurately measure the analyte in the presence of proteins, electrolytes and medications which may interfere.
One of the problems with implantable biosensors occurs as a result of "road block" type interference. This problem is encountered when the outermost layer of the biosensor has some hydrophobic characteristics. These characteristics result in the accumulation of plasma proteins on the surface of the electrode after only short periods of direct contact with body fluids. The hydrophobic regions of the sensor surface are believed to denature the proteins resulting in large deposits of protein mass.
The deposits then affect the sensor's performance through a physical interference in a "road block"
type of effect. The protein deposition is a gradual process which creates a non-uniform, non-predictable diffusion path for the analyte to the sensor. Moreover, the effect on the sensor is a cascading type in which the protein deposits dissapate the normal voltages _ applied to the electrodes (i.e., the deposits increase the capacitance of the system). The resultant requirement for higher voltages to offset the increased capacitance increases the noise, ultimately compromising the validity of the sensor's output.
Other problems are also associated with implantable sensors having hydrophobic regions at the sensor's surface. do particular, subcutaneous tissue contains - substantial amounts of lipid vesicles. By implanting a biosensor directly into tissue, a portion of the sensor may be implanted directly into, or flush against a very hydrophobic lipid region. This also limits the aqueous environment which is required around the sensor's electrodes.
What is needed in the art are new coatings for implantable sensors which are extremely hydrophilic and provide a substantial and uniform aqueous flow around the sensors. Quite surprisingly, the present invention provides such coatings and sensors equipped with those coatings.
SUMMARY OF THE INVENTION
The present invention provides methods for reducing the electrode impedance of implantable biosensors by coating the surface of the biosensor with a uniform hydrogel which allows unimpeded water movement around the sensor. The surface coatings are compositions which are biocompatible and are capable of water uptake of at least 120% of their weight, more preferably at least 200% of their weight. Upon the uptake of water, the hydrogels used in the present invention will also swell and provide a layer of water around the electrodes to which the hydrogels are attached.
In one group of embodiments, the hydrogels can be prepared from:
(a) a diisocyanate, (b) a hydrophilic polymer which is a hydrophilic diol, a hydrophilic diamine, or a combination thereof, and optionally, (c) a chain extender.
In one embodiment, there is provided a method of reducing electrode impedance of an implantable biosensor comprising coating the biosensor with a hydrogel, wherein the hydrogel is formed from a reaction mixture of (a) a diisocyanate, the diisocyanate comprising about 50 mol% of the reactants in said mixture; (b) a hydrophilic polymer which is a member selected from the group consisting of a hydrophilic polymer diol, a hydrophilic polymer diamine and combinations thereof; and optionally; (c) a chain extender, the hydrogel having a water pickup of from about 120% to about 400%
by weight.
In another embodiment, there is provided an implantable biosensor having a hydrogel coating, the coating prepared from a reaction mixture of: (a) a diisocyanate, the diisocyanate comprising about 50 mol% of the reactants in the mixture; (b) a hydrophilic polymer which is a member selected from the group consisting of a hydrophilic polymer diol, a hydrophilic polymer diamine and combinations thereof; and optionally;
(c) a chain extender; wherein the coating has a water pickup of from about 120% to about 400% by weight.
3a The present invention further provides implantable biosensors for measuring a variety of analytes, the biosensor having a coating as described above.
BRIEF DESCRIPTION OF THE DRAWINGS
Figure 1 illustrates polymerization reactions of a diisocyanate with a poly(alkylene) glycol or a diamino poly(alkylene oxide) which results in a polyurethane or polyurea, respectively.
Figures 2 and 3 provide the structure of certain aliphatic and aromatic diisocyanates which are useful in forming the coatings described below.
Figure 4 provides the structures of a number of hydrophilic polymers including poly(alkylene) glycols and diamino poly(alkylene oxides) which are used in polymers described below.
Figure 5 provides the structures of some chain extenders which are useful in the present compositions. This include aliphatic diols, diamines and alkanolamines and further include some aromatic diols and diamines.
Figure 6 illustrates portions of a glucose sensor which can be coated with a hydrophilic swellable coating of the present invention. Figure 6A is a schematic top view of a glucose sensor having electrodes covered with a polymer composition of the invention. Figure 6B is a sectional side view of a working electrode of the sensor which is covered with layers of an enzyme, a glucose-limiting polymer and a hydrogel composition of the invention.
DETAILED DESCRIPTION OF THE INVENTION
The following abbreviations are used herein: dl, deciliter; DEG, diethylene glycol; DMF, dimethyl formamide; PBS, phosphate buffered saline; THF, tetrahydrofuran; DT, deionized; PEG, poly(ethylene)glycol; mv, milIivolts.
As used herein, the term "polyurethane/polyurea" refers to a polymer containing urethane linkages, urea linkages or combinations thereof.
Typically, such polymers are formed by combining diisocyanates with alcohols and/or amines.
For example, combining isophorone diisocyanate with PEG 600 and 1,4-diaminobutane under polymerizing conditions provides a polyurethane/polyurea composition having both urethane (carbamate) linkages and urea linkages (see Figure 1).
Methods for Reducing Electrode Impedance of Biosensors In one aspect, the present invention provides methods for reducing electrode impedance of biosensors by coating the biosensor with an extremely hydrophilic polymer such as a hydrogel or a cellulose acetate. Typically, the polymer is applied to the surface of the sensor by spin coating, dipping or spraying. Methods of spraying including traditional methods as well as microdeposition techniques with an ink jet type of dispenser. Additionally, the polymer can be deposited on a sensor using photo-patterning to place the polymer on only specific portions of the sensor. This coating of the sensor provides a uniform water layer around the sensor which allows for improved diffusion of various analytes to the sensor.
A hydrogel is a highly-interdependent, biphasic matrix consisting of a solid component (usually a polymer, and more commonly a highly cross-linked polymer) that 5 has both hydrophilic and hydrophobic character. Additionally, the matrix has a liquid component (e. g. , water) that is retained in the matrix by intermolecular forces. The hydrophobic character provides the matrix with a degree of water insolubility while the hydrophilic character affords water permeability.
The polymer portion of the hydrogel will contain functionality which is suitable for hydrogen bonding (e. g. , hydroxyl groups, amino groups, ether linkages, carboxylic acids and esters, and the like). Moreover, the affinity for water presented by the hydrogen bonding functionality must be of sufficient degree that the hydrated hydrogel will retain the water within its matrix even upon placement of the hydrogel in a hydrophobic medium such as an oil or lipid matrix. In addition to this binding of water within the hydrogel matrix, the hydrogel should allow water to flow through it when placed in an aqueous environment. A number of hydrogels have been developed for use as contact lenses. These hydrogels keep a layer of water at the surface of the eye to protect the eye from drying out.
The hydrogels used in coating the biosensors will typically be a polyurea, a polyurethane or a polyurethane/polyurea combination. Figure 1 illustrates some of the polymerization reactions which result in the compositions of the present invention.
Hvdrogel components The hydrogels which are used in the present invention are prepared from the reaction of a diisocyanate and a hydrophilic polymer, and optionally, a chain extender. The hydrogels are extremely hydrophilic and will have a water pickup of from about 120 % to about 400 % by weight, more preferably from about 150 % to about 400 % .
The diisocyanates which are useful in this aspect of the invention are those which are typically used in the preparation of biocompatible polyurethanes.
Such diisocyanates are described in detail in Szycher, SEMINAR ON ADVANCES IN
MEDICAL
WO 98/17995 PC~Y~JS97/195I3 GRADE POLYURETHANES, Technomic Publishing, (I995) and include both aromatic and aliphatic diisocyanates (see Figures 2 and 3). Examples of suitable aromatic diisocyana.tes include toluene diisocyanate, 4,4'-diphenylmethane diisocyanate, 3,3'-dimethyl-4,4'-biphenyl diisocyanate, naphthalene diisocyanate and paraphenylene diisocyanate. Suitable aliphatic diisocyanates include, for example, i,6-hexamethylene diisocyanate (HDI), trimethylhexamethylene diisocyanate (TMDI}, traps-1,4-cyclohexane diisocyanate (CHDI), 1,4-cyclohexane bis(methylene isocyanate) (BDI), 1,3-cyclohexane bis(methylene isocyanate) (H6XDI), isophorone diisocyanate (IPDI) and 4,4'-methylenebis(cyclohexyl isocyanate) (H12MDI). In preferred embodiments, the diisocyanate is an aliphatic diisocyanate, more preferably isophorone diisocyanate, 1,6-hexamethylene diisocyanate, -or 4,4'-methylenebis(cyclohexyl isocyanate). A number of these diisocyanates are available from commercial sources such as Aldrich Chemical Company (Milwaukee, Wisconsin, USA) or can be readily prepared by standard synthetic methods using literature procedures.
The quantity of diisocyanate used in the reaction mixture for the present compositions is typically about 50 rnol % relative to the combination of the remaining reactants. More particularly, the quantity of diisocyanate employed in the preparation of =the present compositions will be sufficient to provide at least about 100 %
of the -NCO
groups necessary to react with the hydroxyl or amino groups of the remaining reactants.
For example, a polymer which is prepared using x moles of diisocyanate, will use a moles of a hydrophilic polymer (diol, diamine or combination), arid b moles of a chain extender, such that x = a + b, with the understanding that b can be zero.
A second reactant used in the preparation of the swellable coatings described herein is a hydrophilic polymer. The hydrophilic polymer can be a hydrophilic diol, a hydrophilic diamine or a combination thereof. The hydrophilic diol can be a poly(alkylene)glycol, a polyester-based polyol, or a polycarbonate polyol {see Figure 4).
As used herein, the term "poly(alkylene)glycol" refers to polymers of lower alkylene glycols such as poly(ethylene)glycol, poIy(propylene)glycol and polytetramethylene ether ~Iycol (PTMEG). The term "polyester-based polyol" refers to a polymer as depicted in Figure 4 in which the R group is a lower alkylene group such as ethylene, 1,3-propylene, 1,2-propylene, 1,4-butylene, 2,2-dimethyl-1,3-propylene, and the like. One of skill in the art will also understand that the diester portion of the polymer can also vary from the six-carbon diacid shown. For example, while Figure 4 illustrates an adipic acid component, the present invention also contemplates the use of succinic acid esters, glutaric acid esters and the like. The term "polycarbonate polyol" refers those polymers having hydroxyl functionality at the chain termini and ether and carbonate functionality within the polymer chain (see Figure 4). The alkyl portion of the polymer will typically be composed of C2 to C4 aliphatic radicals, or in some embodiments, Longer chain aliphatic radicals, cycloaliphatic radicals or aromatic radicals. The term "hydrophilic diamines"
refers to any of the above hydrophilic diols in which the terminal hydroxyl groups have been replaced by reactive amine groups or in which the terminal hydroxyl groups have been derivatized to produce an extended chain having terminal amine groups. For example, a preferred hydrophilic diamine is a "diamino poIy(oxyalkylene)" which is poly(alkylene)glycol in which the terminal hydroxyl groups are replaced with amino groups. The term "diamino poly(oxyalkylene" also refers to poly(alkylene)glycols which have aminoalkyl ether groups at the chain termini. One example of a suitable diamino poly{oxyalkylene) is polypropylene glycol) bis(2-aminopropyl ether). A number of diamino poly(oxyalkylenes) are available having different average molecular weights and are sold as Jeffamines~ (for example, Jeffamine 230, Jeffamine 600, Jeffamine 900 and Jeffamine 2000). These polymers can be obtained from Aldrich Chemical Company.
Alternatively, literature methods can be employed fox their synthesis.
The amount of hydrophilic polymer which is used in the present compositions will typically be about 10% to about 100% by mole relative to the diisocyanate which is used. Preferably, the amount is from about 50% to about 90% by mole relative to the diisocyanate. When amounts less than 100% of hydrophilic polymer are used, the remaining percentage (up to I00%) will be a chain extender.
Thus, in one group of embodiments, the reaction mixture for the preparation of swellable coatings will also contain a chain extender which is an aliphatic or aromatic diol, an aliphatic or aromatic diamine, alkanolamine, or combinations thereof (see Figure 8). Examples of suitable aliphatic chain extenders include ethylene glycol, propylene glycol, 1,4-butanediol, 1,6-hexanediol, ethanoiamine, ethylene diamine, butane diamine and 1,4-cyclohexanedirnethanol. Aromatic chain extenders include, for example, para-di(2-hydroxyethoxy)benzene, meta-di(2-hydroxyethoxy)benzene, Ethacure I00~ (a mixture of two isomers of 2,4-diamino-3,5-diethyltoluene), Ethacure 300~ (2,4-diarnino-WO 9$!17995 PCT/LTS97/19513 3,5-di(methylthio)toluene), 3,3'-dichloro-4,4'diaminodiphenylmethane, Polacure~ 740 M
(trimethylene glycol bis(para-aminobenzoate)ester), arid methylenedianiline.
Incorporation of one or more of the above chain extenders typically provides the resulting biocompatible membrane with additional physical strength, but does not substantially alter the hydrophilicity of the polymer. In particularly preferred compositions, the chain extender is butanediol, ethylenediamine, 1,6-hexamethylenediamine, 1,2-diaminocyclohexane or isophorone diamine. In one group of preferred embodiments, the chain extender is present an amount of from about 10 % to 50 % by mole relative to the diisocyanate.
Goatin~ preparation Polymerization of the above reactants can be carried out in bulk or in a solvent system. Use of a catalyst is preferred, though not required. Suitable catalysts include dibutyItin bis(2-ethylhexanoate), dibutyltin diacetate, triethylamine and combinations thereof. Preferably dibutyltin bis(2-ethylhexanoate is used as the catalyst.
Bulk polymerization is typically carried out at an initial temperature of about 25°C
(ambient temperature) to about 50°C, in order to insure adequate mixing of the reactants.
Upon mixing of the reactants, an exothenn is typically observed, with the temperature rising to about 90-120°C. After the initial exotherm, the reaction flask can be heated at from 75°C to 125°C, with 90°C to 100°C being a preferred temperature range. Heating is usually carried out for one to two hours.
Solution polymerization can be carried out in a similar manner. Solvents which are suitable for solution polymerization include, tetrahydrofuran, dimethylformamide, dimethyl sulfoxide, dimethylacetamide, halogenated solvents such as 1,2,3-trichloropropane, and ketones such as 4-methyl-2-pentanone. Preferably, THF is used as the solvent. When polymerization is carried out in a solvent, heating of the .
reaction mixture is typically carried out for at least three to four hours, and preferably at least 10-20 hours. At the end of this time period, the solution polymer is typically cooled to room temperature and poured into DI water. The precipitated polymer is collected, dried, washed with hot DI water to remove solvent and unreacted monomers, then re-dried. The dried polymer can be evaluated for water pickup as described in the Examples below.
The hydrogels which are useful in the present invention will have a water pickup of at least 120 '~ , preferably 150 ~ to about 400 °l6 , and more preferably about 200 °~ to about 400 ~ .
Polymers prepared by bulk polymerization are typically dissolved in dimethylformamide and precipitatai from water. Polymers prepared in solvents such as THF can be poured into water at ambient temperatures, then f ltered, dried, washed with boiling water and re-dried.
Once the polymers have been prepared having suitable water pickup, the polymers can be solubilized in a solvent and used to coat a biosensor.
Preparation of coated biosensors can be accomplished by dissolving the dried polymer in a suitable solvent and spin-coating the sensor, typically using, for example, a 5 wt~ in 2-propanol solution of the polymer. The selection of other suitable solvents for coating the sensors will typically depend on the particular polymer as well as the volatility of the solvent. Other suitable solvents include THF, CHCl3, CHZC12, DMF
or combinations thereof. More preferably, the solvent is THF or DMF/CHZCIZ
(2/98 volume ~).
A number of different 'sensors can be used in the methods and compositions of the presem invention.
Membrane-Coated Biosensors Glucose sensors which utilize, for example, glucose oxidase to effect a reaction of glucose and oxygen are known in the art, and are within the skill in the art to fabricate. See, for example, U.S. Patent Nos. 5,165,407, 4,890,620, 5,390,671 and 5,391,250. ~ ~ 'The present invention depends not on the configuration of the biosensor, but rather on the use of the inventive membranes to cover or encapsulate the sensor elements.
In particular, the hydrogels described herein are particularly useful with a variety of biosensors for which it is advantageous to provide a surrou~ing water layer for the electrodes. Various such biosensors are well known in the art. For example, sensors for monitoring glucose concentration of diabetics are described in Shichiri, et al., : "In Vivo Characteristics of Needle-Type Glucose Sensor-Measurements of Subcutaneous Glucose Concentrations in Human Volunteers,"
Xorm. Metab. Res., Suppl. Ser. 20:17-20 (1988); Bruckel, et al., : "In Vivo Measurement of Subcutaneous. Glucose Concentrations with an Enzymatic Glucose Sensor and a Wick 5 Method, " Klin. Wochenschr. 67:491-495 ( 1989); and Pickup, et al. , : "In .
Vivo Molecular Sensing in Diabetes Mellitus: An Implantable Glucose Sensor with Direct Electron Transfer, " Diabetologia 32:213-217 ( 1989) .
Other sensors are described in, for example Reach, et al. , in ADVANCES ~N
BIOSENSORS, A. Turner (ed.), JAI Press, London, Chap. 1, (1993), The following examples are offered by way of illustration and are not meant to limit the scope of the invention.
EXAMPLES
The materials used in the examples were obtained from the following sources: isophorone diisocyanate, 1,6-hexamethylenediisocyanate, PEG 600, butanediol, ethylene diamine, hexamethylenediamine, isophorone diamine and 1,2-diaminohexane (Aldrich Chemical Co. , Milwaukee, Wisconsin, USA); Jeffamine~ D-230, ED-600, ED-900 and D-2000 were obtained from Aldrich.
General Methods (a) Hydxogel Preparation Hydrogels suitable for use as biosensor coatings were prepared by combining a diisocyanate with an equivalent molar amount of a hydrophilic diol or diamine or with a combination of diol or diamine and chain extender such that the molar amount of the combination was equivalent to the diisocyanate. The polymerizations were carried out in a one-pot reaction using THF as solvent and a Mace catalyst (tributyltin ethylhexanoate). The reactions were heated to reflex and held at this temperature overnight (about 16 hours). The resulting polymer solution was poured into a large volume of DI water at about 20°C and then filtered, dried, and washed with boiling DI
water. The resulting polymer was again dried then taken up in 2-propanol (as a 5 wt l - solution) and used for spin coating.
(b) Coating of biosensors Coating of biosensors can be carried out using a commercial spin coating apparatus operating at between 1000 and 5000 rpm, depending on the viscosity of the polymer solution and the desired thickness of the hydrophilic coating.
(c) Water pickup Water picl.~up was determined gravimetrically at room temperature on polymers which had been dried to a constant weight at 50°C in vacuo, then weighed, immersed in deionized water for 24 hours, removed and blotted with filter paper, and weighed. Percent water pickup was determined from the formula:
Pickup = (W W - W~)/W~ x 100 where WW is the weight of the swollen film and Wd is the weight of the dry film.
i5 (d) Impedance measurements Electrochemical impedance measurements were performed on finished sensors using a Bioanalytical Systems (BAS, Lafayette, Indiana) 100B
Electrochemical Analyzer. Impedance was measured in a three electrode mode from 0.01 Hz to 1000 Hz.
Linear extrapolation to DC impedance was used to obtain the final impedance figures.
The final impedance is calculated as the sum of the real and imaginary parts of the impedance. The measurements were made in 100 mg/dl glucose solution in PBS, with a 600 my applied potential and a 5 my A.C. signal imposed on the applied potential.
This example provides the formulations and properties of representative coatings.
Table I provides ten formulations for representative polymers which were prepared by solution polymerization.
Representative Polymer Formulations Polymer Diisocyanate Hydrophilic diol Chain Extender or diamine 1 1,6-Hexamethylene Jeffamine 600 Butanediol {95%) (5 % ) 2 1,6-Hexamethylene Jeffamine 2000 None -(100% ) 3 1,6-Hexamethylene Jeffamine 2000 Butanediol (90 % ) (10%) 4 1,6-Hexamethylene PEG 2000 Butanediol (90%) (IO%) 5 1,6-Hexamethylene Jeffamine 230 Ethylene diamine (30 % ) ('70 %) 6 I,6-HexamethyIene PEG 600 Ethylene diamine (75 %) (25 %) 7 Isophorone PEG 600 Butanediol (75%) (25%) 8 Isophorone Jeffamine 900 I,6-Diaminohexane (70 % ) (25 % ) 9 Isophorone Jeffamine 900 1,2-Diaminocyclo-(50 % ) hexane (50 % ) 1~ Isophorone Jeffamine 900 Isophorone diamine (50 % ) (50 % ) A
WO 98!17995 PCT/US97/19513 above.
Table 2 provides certain physical and chemical properties of the polymers Physical Properties of Representative Polymers Polymer Water Pickup (%) Impedance (Ohms) (x lOfi) I 250 2.3 2 160 1.7 3 240 1.4 4 400 6.1 5 110 3.3 6 45 6.9 7 280 1. I
S 240 0.7 9 220 0.5 10 184 0.$
This example illustrates the evaluation of a membrane-coated biosensor constructed according to the present invention.
A membrane. prepared from the polymer identified as 9 above was found to have excellent mechanical properties as well as appropriate water uptake and oxygen and glucose diffusivities. The membrane was evaluated using a prototype glucose sensor illustrated in Figure 6A. According to Figure 6A, a sensor 20 was constructed having a reference electrode 22, a working electrode 24, and a counter electrode 26 deposited on a polymeric sheet 29. A series of bonding pads 28 complete the sensor 20. As shown in Figure 6B, the working electrode 24 was covered with a layer 30 of the enzyme glucose oxidase and the entire electrode array was coated with a first layer 32 of a glucose-limiting polymer prepared according to U.S. Patent 5,777,060 and a second layer 34 of the polymer 9 (see Example 1) by spin coating. The glucose limiting polymer was applied from a 7 wt % solution of the polymer in TI3F and the hydrophilic coating 34 was applied from a 5 wt % solution in 2-propanol. The sensor was connected to a commercial potentiostat (BAS Instruments, not shown) and operated with a potential of +0.6 volts between the working electrode and the reference electrode.
The above description is illustrative and not restrictive. Many variations of the invention will become apparent to those of skill in the art upon review of this disclosure. Merely by way of example a variety of solvents, membrane formation methods, and other materials may be used without departing from the scope of the invention. The scope of the invention should, therefore, be determined not with reference to the above description, but instead should be determined with reference to the appended claims along with their full scope of equivalents.
Figure 6 illustrates portions of a glucose sensor which can be coated with a hydrophilic swellable coating of the present invention. Figure 6A is a schematic top view of a glucose sensor having electrodes covered with a polymer composition of the invention. Figure 6B is a sectional side view of a working electrode of the sensor which is covered with layers of an enzyme, a glucose-limiting polymer and a hydrogel composition of the invention.
DETAILED DESCRIPTION OF THE INVENTION
The following abbreviations are used herein: dl, deciliter; DEG, diethylene glycol; DMF, dimethyl formamide; PBS, phosphate buffered saline; THF, tetrahydrofuran; DT, deionized; PEG, poly(ethylene)glycol; mv, milIivolts.
As used herein, the term "polyurethane/polyurea" refers to a polymer containing urethane linkages, urea linkages or combinations thereof.
Typically, such polymers are formed by combining diisocyanates with alcohols and/or amines.
For example, combining isophorone diisocyanate with PEG 600 and 1,4-diaminobutane under polymerizing conditions provides a polyurethane/polyurea composition having both urethane (carbamate) linkages and urea linkages (see Figure 1).
Methods for Reducing Electrode Impedance of Biosensors In one aspect, the present invention provides methods for reducing electrode impedance of biosensors by coating the biosensor with an extremely hydrophilic polymer such as a hydrogel or a cellulose acetate. Typically, the polymer is applied to the surface of the sensor by spin coating, dipping or spraying. Methods of spraying including traditional methods as well as microdeposition techniques with an ink jet type of dispenser. Additionally, the polymer can be deposited on a sensor using photo-patterning to place the polymer on only specific portions of the sensor. This coating of the sensor provides a uniform water layer around the sensor which allows for improved diffusion of various analytes to the sensor.
A hydrogel is a highly-interdependent, biphasic matrix consisting of a solid component (usually a polymer, and more commonly a highly cross-linked polymer) that 5 has both hydrophilic and hydrophobic character. Additionally, the matrix has a liquid component (e. g. , water) that is retained in the matrix by intermolecular forces. The hydrophobic character provides the matrix with a degree of water insolubility while the hydrophilic character affords water permeability.
The polymer portion of the hydrogel will contain functionality which is suitable for hydrogen bonding (e. g. , hydroxyl groups, amino groups, ether linkages, carboxylic acids and esters, and the like). Moreover, the affinity for water presented by the hydrogen bonding functionality must be of sufficient degree that the hydrated hydrogel will retain the water within its matrix even upon placement of the hydrogel in a hydrophobic medium such as an oil or lipid matrix. In addition to this binding of water within the hydrogel matrix, the hydrogel should allow water to flow through it when placed in an aqueous environment. A number of hydrogels have been developed for use as contact lenses. These hydrogels keep a layer of water at the surface of the eye to protect the eye from drying out.
The hydrogels used in coating the biosensors will typically be a polyurea, a polyurethane or a polyurethane/polyurea combination. Figure 1 illustrates some of the polymerization reactions which result in the compositions of the present invention.
Hvdrogel components The hydrogels which are used in the present invention are prepared from the reaction of a diisocyanate and a hydrophilic polymer, and optionally, a chain extender. The hydrogels are extremely hydrophilic and will have a water pickup of from about 120 % to about 400 % by weight, more preferably from about 150 % to about 400 % .
The diisocyanates which are useful in this aspect of the invention are those which are typically used in the preparation of biocompatible polyurethanes.
Such diisocyanates are described in detail in Szycher, SEMINAR ON ADVANCES IN
MEDICAL
WO 98/17995 PC~Y~JS97/195I3 GRADE POLYURETHANES, Technomic Publishing, (I995) and include both aromatic and aliphatic diisocyanates (see Figures 2 and 3). Examples of suitable aromatic diisocyana.tes include toluene diisocyanate, 4,4'-diphenylmethane diisocyanate, 3,3'-dimethyl-4,4'-biphenyl diisocyanate, naphthalene diisocyanate and paraphenylene diisocyanate. Suitable aliphatic diisocyanates include, for example, i,6-hexamethylene diisocyanate (HDI), trimethylhexamethylene diisocyanate (TMDI}, traps-1,4-cyclohexane diisocyanate (CHDI), 1,4-cyclohexane bis(methylene isocyanate) (BDI), 1,3-cyclohexane bis(methylene isocyanate) (H6XDI), isophorone diisocyanate (IPDI) and 4,4'-methylenebis(cyclohexyl isocyanate) (H12MDI). In preferred embodiments, the diisocyanate is an aliphatic diisocyanate, more preferably isophorone diisocyanate, 1,6-hexamethylene diisocyanate, -or 4,4'-methylenebis(cyclohexyl isocyanate). A number of these diisocyanates are available from commercial sources such as Aldrich Chemical Company (Milwaukee, Wisconsin, USA) or can be readily prepared by standard synthetic methods using literature procedures.
The quantity of diisocyanate used in the reaction mixture for the present compositions is typically about 50 rnol % relative to the combination of the remaining reactants. More particularly, the quantity of diisocyanate employed in the preparation of =the present compositions will be sufficient to provide at least about 100 %
of the -NCO
groups necessary to react with the hydroxyl or amino groups of the remaining reactants.
For example, a polymer which is prepared using x moles of diisocyanate, will use a moles of a hydrophilic polymer (diol, diamine or combination), arid b moles of a chain extender, such that x = a + b, with the understanding that b can be zero.
A second reactant used in the preparation of the swellable coatings described herein is a hydrophilic polymer. The hydrophilic polymer can be a hydrophilic diol, a hydrophilic diamine or a combination thereof. The hydrophilic diol can be a poly(alkylene)glycol, a polyester-based polyol, or a polycarbonate polyol {see Figure 4).
As used herein, the term "poly(alkylene)glycol" refers to polymers of lower alkylene glycols such as poly(ethylene)glycol, poIy(propylene)glycol and polytetramethylene ether ~Iycol (PTMEG). The term "polyester-based polyol" refers to a polymer as depicted in Figure 4 in which the R group is a lower alkylene group such as ethylene, 1,3-propylene, 1,2-propylene, 1,4-butylene, 2,2-dimethyl-1,3-propylene, and the like. One of skill in the art will also understand that the diester portion of the polymer can also vary from the six-carbon diacid shown. For example, while Figure 4 illustrates an adipic acid component, the present invention also contemplates the use of succinic acid esters, glutaric acid esters and the like. The term "polycarbonate polyol" refers those polymers having hydroxyl functionality at the chain termini and ether and carbonate functionality within the polymer chain (see Figure 4). The alkyl portion of the polymer will typically be composed of C2 to C4 aliphatic radicals, or in some embodiments, Longer chain aliphatic radicals, cycloaliphatic radicals or aromatic radicals. The term "hydrophilic diamines"
refers to any of the above hydrophilic diols in which the terminal hydroxyl groups have been replaced by reactive amine groups or in which the terminal hydroxyl groups have been derivatized to produce an extended chain having terminal amine groups. For example, a preferred hydrophilic diamine is a "diamino poIy(oxyalkylene)" which is poly(alkylene)glycol in which the terminal hydroxyl groups are replaced with amino groups. The term "diamino poly(oxyalkylene" also refers to poly(alkylene)glycols which have aminoalkyl ether groups at the chain termini. One example of a suitable diamino poly{oxyalkylene) is polypropylene glycol) bis(2-aminopropyl ether). A number of diamino poly(oxyalkylenes) are available having different average molecular weights and are sold as Jeffamines~ (for example, Jeffamine 230, Jeffamine 600, Jeffamine 900 and Jeffamine 2000). These polymers can be obtained from Aldrich Chemical Company.
Alternatively, literature methods can be employed fox their synthesis.
The amount of hydrophilic polymer which is used in the present compositions will typically be about 10% to about 100% by mole relative to the diisocyanate which is used. Preferably, the amount is from about 50% to about 90% by mole relative to the diisocyanate. When amounts less than 100% of hydrophilic polymer are used, the remaining percentage (up to I00%) will be a chain extender.
Thus, in one group of embodiments, the reaction mixture for the preparation of swellable coatings will also contain a chain extender which is an aliphatic or aromatic diol, an aliphatic or aromatic diamine, alkanolamine, or combinations thereof (see Figure 8). Examples of suitable aliphatic chain extenders include ethylene glycol, propylene glycol, 1,4-butanediol, 1,6-hexanediol, ethanoiamine, ethylene diamine, butane diamine and 1,4-cyclohexanedirnethanol. Aromatic chain extenders include, for example, para-di(2-hydroxyethoxy)benzene, meta-di(2-hydroxyethoxy)benzene, Ethacure I00~ (a mixture of two isomers of 2,4-diamino-3,5-diethyltoluene), Ethacure 300~ (2,4-diarnino-WO 9$!17995 PCT/LTS97/19513 3,5-di(methylthio)toluene), 3,3'-dichloro-4,4'diaminodiphenylmethane, Polacure~ 740 M
(trimethylene glycol bis(para-aminobenzoate)ester), arid methylenedianiline.
Incorporation of one or more of the above chain extenders typically provides the resulting biocompatible membrane with additional physical strength, but does not substantially alter the hydrophilicity of the polymer. In particularly preferred compositions, the chain extender is butanediol, ethylenediamine, 1,6-hexamethylenediamine, 1,2-diaminocyclohexane or isophorone diamine. In one group of preferred embodiments, the chain extender is present an amount of from about 10 % to 50 % by mole relative to the diisocyanate.
Goatin~ preparation Polymerization of the above reactants can be carried out in bulk or in a solvent system. Use of a catalyst is preferred, though not required. Suitable catalysts include dibutyItin bis(2-ethylhexanoate), dibutyltin diacetate, triethylamine and combinations thereof. Preferably dibutyltin bis(2-ethylhexanoate is used as the catalyst.
Bulk polymerization is typically carried out at an initial temperature of about 25°C
(ambient temperature) to about 50°C, in order to insure adequate mixing of the reactants.
Upon mixing of the reactants, an exothenn is typically observed, with the temperature rising to about 90-120°C. After the initial exotherm, the reaction flask can be heated at from 75°C to 125°C, with 90°C to 100°C being a preferred temperature range. Heating is usually carried out for one to two hours.
Solution polymerization can be carried out in a similar manner. Solvents which are suitable for solution polymerization include, tetrahydrofuran, dimethylformamide, dimethyl sulfoxide, dimethylacetamide, halogenated solvents such as 1,2,3-trichloropropane, and ketones such as 4-methyl-2-pentanone. Preferably, THF is used as the solvent. When polymerization is carried out in a solvent, heating of the .
reaction mixture is typically carried out for at least three to four hours, and preferably at least 10-20 hours. At the end of this time period, the solution polymer is typically cooled to room temperature and poured into DI water. The precipitated polymer is collected, dried, washed with hot DI water to remove solvent and unreacted monomers, then re-dried. The dried polymer can be evaluated for water pickup as described in the Examples below.
The hydrogels which are useful in the present invention will have a water pickup of at least 120 '~ , preferably 150 ~ to about 400 °l6 , and more preferably about 200 °~ to about 400 ~ .
Polymers prepared by bulk polymerization are typically dissolved in dimethylformamide and precipitatai from water. Polymers prepared in solvents such as THF can be poured into water at ambient temperatures, then f ltered, dried, washed with boiling water and re-dried.
Once the polymers have been prepared having suitable water pickup, the polymers can be solubilized in a solvent and used to coat a biosensor.
Preparation of coated biosensors can be accomplished by dissolving the dried polymer in a suitable solvent and spin-coating the sensor, typically using, for example, a 5 wt~ in 2-propanol solution of the polymer. The selection of other suitable solvents for coating the sensors will typically depend on the particular polymer as well as the volatility of the solvent. Other suitable solvents include THF, CHCl3, CHZC12, DMF
or combinations thereof. More preferably, the solvent is THF or DMF/CHZCIZ
(2/98 volume ~).
A number of different 'sensors can be used in the methods and compositions of the presem invention.
Membrane-Coated Biosensors Glucose sensors which utilize, for example, glucose oxidase to effect a reaction of glucose and oxygen are known in the art, and are within the skill in the art to fabricate. See, for example, U.S. Patent Nos. 5,165,407, 4,890,620, 5,390,671 and 5,391,250. ~ ~ 'The present invention depends not on the configuration of the biosensor, but rather on the use of the inventive membranes to cover or encapsulate the sensor elements.
In particular, the hydrogels described herein are particularly useful with a variety of biosensors for which it is advantageous to provide a surrou~ing water layer for the electrodes. Various such biosensors are well known in the art. For example, sensors for monitoring glucose concentration of diabetics are described in Shichiri, et al., : "In Vivo Characteristics of Needle-Type Glucose Sensor-Measurements of Subcutaneous Glucose Concentrations in Human Volunteers,"
Xorm. Metab. Res., Suppl. Ser. 20:17-20 (1988); Bruckel, et al., : "In Vivo Measurement of Subcutaneous. Glucose Concentrations with an Enzymatic Glucose Sensor and a Wick 5 Method, " Klin. Wochenschr. 67:491-495 ( 1989); and Pickup, et al. , : "In .
Vivo Molecular Sensing in Diabetes Mellitus: An Implantable Glucose Sensor with Direct Electron Transfer, " Diabetologia 32:213-217 ( 1989) .
Other sensors are described in, for example Reach, et al. , in ADVANCES ~N
BIOSENSORS, A. Turner (ed.), JAI Press, London, Chap. 1, (1993), The following examples are offered by way of illustration and are not meant to limit the scope of the invention.
EXAMPLES
The materials used in the examples were obtained from the following sources: isophorone diisocyanate, 1,6-hexamethylenediisocyanate, PEG 600, butanediol, ethylene diamine, hexamethylenediamine, isophorone diamine and 1,2-diaminohexane (Aldrich Chemical Co. , Milwaukee, Wisconsin, USA); Jeffamine~ D-230, ED-600, ED-900 and D-2000 were obtained from Aldrich.
General Methods (a) Hydxogel Preparation Hydrogels suitable for use as biosensor coatings were prepared by combining a diisocyanate with an equivalent molar amount of a hydrophilic diol or diamine or with a combination of diol or diamine and chain extender such that the molar amount of the combination was equivalent to the diisocyanate. The polymerizations were carried out in a one-pot reaction using THF as solvent and a Mace catalyst (tributyltin ethylhexanoate). The reactions were heated to reflex and held at this temperature overnight (about 16 hours). The resulting polymer solution was poured into a large volume of DI water at about 20°C and then filtered, dried, and washed with boiling DI
water. The resulting polymer was again dried then taken up in 2-propanol (as a 5 wt l - solution) and used for spin coating.
(b) Coating of biosensors Coating of biosensors can be carried out using a commercial spin coating apparatus operating at between 1000 and 5000 rpm, depending on the viscosity of the polymer solution and the desired thickness of the hydrophilic coating.
(c) Water pickup Water picl.~up was determined gravimetrically at room temperature on polymers which had been dried to a constant weight at 50°C in vacuo, then weighed, immersed in deionized water for 24 hours, removed and blotted with filter paper, and weighed. Percent water pickup was determined from the formula:
Pickup = (W W - W~)/W~ x 100 where WW is the weight of the swollen film and Wd is the weight of the dry film.
i5 (d) Impedance measurements Electrochemical impedance measurements were performed on finished sensors using a Bioanalytical Systems (BAS, Lafayette, Indiana) 100B
Electrochemical Analyzer. Impedance was measured in a three electrode mode from 0.01 Hz to 1000 Hz.
Linear extrapolation to DC impedance was used to obtain the final impedance figures.
The final impedance is calculated as the sum of the real and imaginary parts of the impedance. The measurements were made in 100 mg/dl glucose solution in PBS, with a 600 my applied potential and a 5 my A.C. signal imposed on the applied potential.
This example provides the formulations and properties of representative coatings.
Table I provides ten formulations for representative polymers which were prepared by solution polymerization.
Representative Polymer Formulations Polymer Diisocyanate Hydrophilic diol Chain Extender or diamine 1 1,6-Hexamethylene Jeffamine 600 Butanediol {95%) (5 % ) 2 1,6-Hexamethylene Jeffamine 2000 None -(100% ) 3 1,6-Hexamethylene Jeffamine 2000 Butanediol (90 % ) (10%) 4 1,6-Hexamethylene PEG 2000 Butanediol (90%) (IO%) 5 1,6-Hexamethylene Jeffamine 230 Ethylene diamine (30 % ) ('70 %) 6 I,6-HexamethyIene PEG 600 Ethylene diamine (75 %) (25 %) 7 Isophorone PEG 600 Butanediol (75%) (25%) 8 Isophorone Jeffamine 900 I,6-Diaminohexane (70 % ) (25 % ) 9 Isophorone Jeffamine 900 1,2-Diaminocyclo-(50 % ) hexane (50 % ) 1~ Isophorone Jeffamine 900 Isophorone diamine (50 % ) (50 % ) A
WO 98!17995 PCT/US97/19513 above.
Table 2 provides certain physical and chemical properties of the polymers Physical Properties of Representative Polymers Polymer Water Pickup (%) Impedance (Ohms) (x lOfi) I 250 2.3 2 160 1.7 3 240 1.4 4 400 6.1 5 110 3.3 6 45 6.9 7 280 1. I
S 240 0.7 9 220 0.5 10 184 0.$
This example illustrates the evaluation of a membrane-coated biosensor constructed according to the present invention.
A membrane. prepared from the polymer identified as 9 above was found to have excellent mechanical properties as well as appropriate water uptake and oxygen and glucose diffusivities. The membrane was evaluated using a prototype glucose sensor illustrated in Figure 6A. According to Figure 6A, a sensor 20 was constructed having a reference electrode 22, a working electrode 24, and a counter electrode 26 deposited on a polymeric sheet 29. A series of bonding pads 28 complete the sensor 20. As shown in Figure 6B, the working electrode 24 was covered with a layer 30 of the enzyme glucose oxidase and the entire electrode array was coated with a first layer 32 of a glucose-limiting polymer prepared according to U.S. Patent 5,777,060 and a second layer 34 of the polymer 9 (see Example 1) by spin coating. The glucose limiting polymer was applied from a 7 wt % solution of the polymer in TI3F and the hydrophilic coating 34 was applied from a 5 wt % solution in 2-propanol. The sensor was connected to a commercial potentiostat (BAS Instruments, not shown) and operated with a potential of +0.6 volts between the working electrode and the reference electrode.
The above description is illustrative and not restrictive. Many variations of the invention will become apparent to those of skill in the art upon review of this disclosure. Merely by way of example a variety of solvents, membrane formation methods, and other materials may be used without departing from the scope of the invention. The scope of the invention should, therefore, be determined not with reference to the above description, but instead should be determined with reference to the appended claims along with their full scope of equivalents.
Claims (15)
1. A method of reducing electrode impedance of an implantable biosensor comprising coating said biosensor with a hydrogel, wherein said hydrogel is formed from a reaction mixture of:
(a) a diisocyanate, said diisocyanate comprising about 50 mol% of the reactants in said mixture;
(b) a hydrophilic polymer which is a member selected from the group consisting of a hydrophilic polymer diol, a hydrophilic polymer diamine and combinations thereof; and optionally;
(c) a chain extender, said hydrogel having a water pickup of from about 120%
to about 400% by weight.
(a) a diisocyanate, said diisocyanate comprising about 50 mol% of the reactants in said mixture;
(b) a hydrophilic polymer which is a member selected from the group consisting of a hydrophilic polymer diol, a hydrophilic polymer diamine and combinations thereof; and optionally;
(c) a chain extender, said hydrogel having a water pickup of from about 120%
to about 400% by weight.
2. A method in accordance with claim 1, wherein said coating is by spin coating, dipping or spraying.
3. A method in accordance with claim 1 or 2, wherein said hydrophilic polymer is a poly(ethylene)glycol or a diaminopoly(oxyalkylene) selected from the group consisting of PEG
600, PEG 2000, Jeffamine .TM. D-230, Jeffamine .TM. ED-600, Jeffamine .TM. ED-900 and Jeffamine .TM. D-2000.
600, PEG 2000, Jeffamine .TM. D-230, Jeffamine .TM. ED-600, Jeffamine .TM. ED-900 and Jeffamine .TM. D-2000.
4. A method in accordance with any one of claims 1 to 3, wherein said diisocyanate is a member selected from the group consisting of isophorone diisocyanate, 1,6-hexamethylene diisocyanate and 4,4'methylenebis(cyclohexyl isocyanate).
5. A method in accordance with any one of claims 1 to 4, wherein said chain extender is selected from the group consisting of an alkylene diol, an alkylene diamine, an aminoalkanol and combinations thereof.
6. A method in accordance with any one of claims 1 to 4, wherein said chain extender is selected from the group consisting of butanediol, ethylenediamine, hexamethylenediamine, 1,2-diaminocyclohexane and isophoronediamine.
7. A method in accordance with any one of claims 1 to 6, wherein said diisocyanate is 1,6 hexamethylene diisocyanate and said hydrophilic polymer is selected from the group consisting of Jeffamine .TM. ED-600, Jeffamine .TM. D-2000 and PEG 2000 and is present in an amount of about 40 to about 50 mol%.
8. A method in accordance with any one of claims 1 to 4, wherein said diisocyanate is 1,6 hexamethylene diisocyanate, said hydrophilic polymer is selected from the group consisting of Jeffamine .TM. ED-600, Jeffamine .TM. D-2000 and PEG 2000 and is present in an amount of about 40 to about 47.5 mol% and said chain extender is butanediol and is present in an amount of about 2.5 to about 10 mol%.
9. An implantable biosensor having a hydrogel coating, said coating prepared from a reaction mixture of: (a) a diisocyanate, said diisocyanate comprising about 50 mol% of the reactants in said mixture; (b) a hydrophilic polymer which is a member selected from the group consisting of a hydrophilic polymer diol, a hydrophilic polymer diamine and combinations thereof; and optionally; (c) a chain extender; wherein said coating has a water pickup of from about 120% to about 400% by weight.
10. An implantable biosensor in accordance with claim 9, wherein said hydrophilic polymer is a poly(ethylene)glycol or a diaminopoly(oxyalkylene) selected from the group consisting of PEG 600, PEG 2000, Jeffamine .TM. D-230, Jeffamine .TM. ED-600, Jeffamine .TM.
ED-900 and Jeffamine .TM. D-2000.
ED-900 and Jeffamine .TM. D-2000.
11. An implantable biosensor in accordance with claim 9 or 10, wherein said diisocyanate is a member selected from the group consisting of isophorone diisocyanate, 1,6-hexamethylene diisocyanate and 4,4'-methylenebis(cyclohexyl isocyanate).
12. An implantable biosensor in accordance with any one of claims 9 to 11, wherein said chain extender is selected from the group consisting of an alkylene diol, an alkylene diamine, an aminoalkanol and combinations thereof.
13. An implantable biosensor in accordance with any one of claims 9 to 11, wherein said chain extender is selected from the group consisting of butanediol, ethylenediamine, hexamethylenediamine, 1,2-diaminocyclohexane and isophoronediamine.
14. An implantable biosensor in accordance with any one of claims 9 to 13, wherein said diisocyanate is 1,6-hexamethylene diisocyanate and said hydrophilic polymer is selected from the group consisting of Jeffamine .TM. ED-600, Jeffamine .TM. D-2000 and PEG
2000 and is present in an amount of about 40 to about 50 mol%.
2000 and is present in an amount of about 40 to about 50 mol%.
15. An implantable biosensor in accordance with any one of claims 9 to 11, wherein said diisocyanate is 1,6-hexamethylene diisocyanate, said hydrophilic polymer is selected from the group consisting of Jeffamine .TM. ED-600, Jeffamine .TM. D-2000 and PEG 2000 and is present in an amount of about 40 to about 47.5 mol% and said chain extender is butanediol and is present in an amount of about 2.5 to about 10 mol%.
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US08/749,754 | 1996-10-24 | ||
US08/749,754 US5786439A (en) | 1996-10-24 | 1996-10-24 | Hydrophilic, swellable coatings for biosensors |
PCT/US1997/019513 WO1998017995A1 (en) | 1996-10-24 | 1997-10-24 | Hydrophilic, swellable coatings for biosensors |
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CA2238648A1 CA2238648A1 (en) | 1998-04-30 |
CA2238648C true CA2238648C (en) | 2007-03-13 |
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Application Number | Title | Priority Date | Filing Date |
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CA002238648A Expired - Fee Related CA2238648C (en) | 1996-10-24 | 1997-10-24 | Hydrophilic, swellable coatings for biosensors |
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US (3) | US5786439A (en) |
EP (1) | EP0876604B1 (en) |
JP (1) | JP3852712B2 (en) |
AT (1) | ATE327504T1 (en) |
AU (1) | AU5092198A (en) |
CA (1) | CA2238648C (en) |
DE (1) | DE69735932T2 (en) |
DK (1) | DK0876604T3 (en) |
WO (1) | WO1998017995A1 (en) |
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US6462162B2 (en) | 2002-10-08 |
WO1998017995A1 (en) | 1998-04-30 |
AU5092198A (en) | 1998-05-15 |
US20010008931A1 (en) | 2001-07-19 |
US5786439A (en) | 1998-07-28 |
JP3852712B2 (en) | 2006-12-06 |
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