Patent Application
20100174245
This subject invention relates to plasma generation systems and catheter treatment systems and methods.
Catheters for various uses, especially polymer catheters, are often pretreated for a variety of reasons using a variety of methods. For example, polymer based medical catheters are pretreated so that biomedical molecules can better bond with the catheter and/or to increase the wettability of the catheter. Without pretreatment, the polymer surfaces of catheters are too inert or have generally inadequate surface properties for attaching coatings or other surface medication. In general, catheters are pretreated to physically and/or chemically modify them. Plasma is often used in the treatment process.
Given the small interior diameter of a typical catheter, it is difficult to pretreat the lumen of a catheter. See U.S. Pat. No. 5,693,196 incorporated herein which describes the difficulty in forming a plasma in the lumen of small diameter tubing. U.S. Pat. No. 5,486,357 describes treating polymeric surfaces, such as lumens of medical tubing, with a radio frequency generated plasma. The use of a radio frequency generated plasma, however, provides a lesser degree of spatial control for treating a surface and, in addition, a very restricted range of plasma parameters. A RF glow discharge as taught by U.S. Pat. No. 5,914,115 is difficult to maintain within the lumen of a tubular article, especially one having a small diameter. Also, a plasma generated by a RF glow discharge is usually not able to pretreat the lumen of a small diameter polymeric catheter. Microwave chemical vapor deposition also does not work very well for treating small diameter catheters.
The electron cyclotron resonance (ECR) plasma technique has promise over conventional methods, but the ECR process must be applied in the appropriate manner to produce the desired results. Published U.S. Patent Application Serial No. 2002/0172780 by the applicant hereof (incorporated herein by this reference) disclosed an earlier ECR treatment method. The subject invention relates to improvements to an ECR plasma technique for treating the lumen (and optionally the exterior) of a catheter.
It is therefore an object of this invention to provide a new system for and a method of pretreating the lumen of a catheter.
It is a further object of this invention to provide such a system and method which is able to treat multiple catheters at the same time.
It is a further object of this invention to provide such a system and method able to treat the outside as well as the inside of a catheter.
It is a further object of this invention to provide such a system and method which provide more efficient coupling of the microwave power to initiate and maintain a plasma inside a catheter.
The subject invention results from the realization, in part, that circularly polarized microwaves propagated into magnetic field lines co-linear with the propagation direction of the microwaves result in a more efficient coupling of the microwave power to initiate and maintain a plasma inside a catheter to pretreat the same.
The subject invention, however, in other embodiments, need not achieve all these objectives and the claims hereof should not be limited to structures or methods capable of achieving these objectives.
This subject invention features a system for pretreating the lumen of a catheter or small diameter tubing. One preferred system includes a vacuum chamber including a microwave port, and a microwave supply subsystem with a microwave generator and a circular polarizer producing circularly polarized microwaves propagated into the vacuum chamber via the port at a frequency which produces electron cyclotron resonance. A magnetic coil about the vacuum chamber generates a magnetic field in the vacuum chamber with magnetic field lines co-linear with the propagation direction of the microwaves. A manifold fixture positions at least one catheter in the vacuum chamber and supplies a gas within the catheter lumen to generate a plasma in the lumen for pretreating the same. Typically, if the microwaves are right-handed circularly polarized, the magnetic field is parallel to the microwave propagation direction. If the microwaves are left-handed circularly polarized, the magnetic field is anti-parallel to the microwave propagation direction.
One catheter manifold includes a proximal fixture for one end of the catheter and a distal fixture for the other end of the catheter, the distal fixture connected to a gas outlet conduit. The proximal fixture may include a main gear driving a planetary gear fixed to a proximal connector for rotating the catheter for a more uniform plasma treatment. Typically, there are multiple connectors each rotated via a planetary gear.
The microwave generator may produce microwaves at a frequency between 1 GHz and 30 GHz, preferably a frequency of 2.45 GHz. In one example, the magnetic coil is wound to produce a magnetic field axially decreasing in strength producing a magnetic beach in the vacuum chamber aiding in microwave transmission and heating the plasma. Also, the catheter manifold may include means for rotating the catheter and/or for linearly translating the catheter within the vacuum chamber.
The subject invention also features a method of pretreating a lumen of a polymer catheter so it can be coated with a bioactive material. One method includes generating circularly polarized microwaves at a frequency which produces electron cyclotron resonance and propagating the microwaves to a plasma zone, producing a magnetic field in the plasma zone with magnetic field lines co-linear with the propagation direction of the microwaves, and subjecting the polymer catheter to the plasma zone and introducing a gas in the lumen thereof generating plasma in the lumen which pretreats the same. The method may further include pretreating the outer surface of the polymer catheter.
The method may further include the step of coating the pretreated polymer catheter with a bioactive material and/or an anti-microbial material. Examples of bioactive materials include anti-thrombogenic material such as heparin, antithrombin-III—heparin (ATH), collagen, poly hexamethylene biguanide hydrochloride, adenosine diphosphatase (ADPase), tissue factor pathway inhibitor (TFPI), nitric oxide, polyethylene oxide, and/or tetraethylene glycol ether (tetraglyme), thrombomodulin, pentasaccharides, hirulog, hirudin, PPACK, phosphorl choline, plasminogen activators, peptides, heparin cofactor II, aspirin anhydrides, polyethylene oxide conjugated compounds, and mixtures of the above. Examples of anti-microbial materials include selenium, silver, penicillin, tetracycline, sulfa drugs, quaternary ammonium compounds, and/or octenidine dihydrochloride.
The method may further include the step of coating the pretreated polymer catheter with a monomer base layer for coupling with a bioactive material. Examples of monomer base layers include glycidyl methacylate, acrylic acid, acrylamide, allyl alcohol, allyl amine, methacryl chloride, isocyanate ethyl methacrylate ammonium, fluorohydrocarbons, glycidy acrylate, acryloyl chloride and/or modified albumin. The catheters may be fabricated of various polymers including polyurethane, silicone rubber, polyethylene, polypropylene, polycarbonate, polyester, polystyrene, polymethyl methacrylate, and their co-polymers and/or fluorinated hydrocarbons.
The step of generating circularly polarized microwaves may include employing a magnetron generator with a hybrid polarizer to convert linearly polarized microwaves to circular polarization. The generator operates at a frequency between 1 GHz and 30 GHz, typically 2.45 GHz. One preferred method includes creating a magnetic beach.
The plasma may be formed in a flowing or static gas and the plasma zone is defined by the lumen wall of a catheter. In addition, the plasma may be formed in a flowing or static gas and the plasma zone is defined by the vacuum chamber. In one example, the vacuum chamber is vertically oriented with an external solenoid magnet for producing the magnetic field. The step of introducing a gas may include the use of a differential pumping system connected both to a vacuum chamber and to the catheter lumen to cause plasma formation within the lumen region. The step of introducing a gas may also include introducing a Penning gas mixture into the lumen to assist in the initiation of the plasma. Examples of Penning gas mixtures include mixtures of argon and helium, neon and helium, argon and neon, neon and krypton, and/or argon and krypton.
One preferred method includes inserting a fine metallic wire (e.g., titanium) into the catheter lumen to assist in the initiation of the plasma and/or adding a material such as titanium powder or titanium oxide to the lumen wall to assist in the initiation of the plasma.
One method includes the step of rotating the catheter around its longitudinal axis for a more uniform plasma surface treatment and/or longitudinally translating the catheter for a more uniform external plasma surface treatment. In one example, the microwaves are right-handed circularly polarized and the magnetic field is parallel to the microwave propagation direction. In one example, the microwaves are left-handed circularly polarized and the magnetic field is anti-parallel to the microwave propagation direction.
The subject invention also features a polymer catheter pretreated by the method so described. A polymer catheter is pretreated by coating the same with hydrophilic compounds. Hydrophilic compounds include poly ethylene glycol, hyaluronic acid polysaccharides, polyvinyl alcohol, polyisopropyl allylamide, polyvinyl pyrrolidinone, star polymers and/or dendrimers derived from the same. A polymer catheter is also pretreated by coating the same with hydrophobic compounds. Hydrophobic compounds include fluorocarbons, saturated hydrocarbons, and their self assembled monlayers.
Other objects, features and advantages will occur to those skilled in the art from the following description of a preferred embodiment and the accompanying drawings, in which:
Aside from the preferred embodiment or embodiments disclosed below, this invention is capable of other embodiments and of being practiced or being carried out in various ways. Thus, it is to be understood that the invention is not limited in its application to the details of construction and the arrangements of components set forth in the following description or illustrated in the drawings. If only one embodiment is described herein, the claims hereof are not to be limited to that embodiment. Moreover, the claims hereof are not to be read restrictively unless there is clear and convincing evidence manifesting a certain exclusion, restriction, or disclaimer.
Magnetic coil 30,
Catheter manifold 40 positions one or numerous catheters 42a-d and the like within vacuum chamber 10 and supplies a gas or gas mixture within the lumens of the catheters to generate a plasma therein for pretreating the interior of the catheters. Penning mixtures may be used. Other examples include all of the stable noble gases: He, Ne, Ar, Kr, Xe; relatively inert gases (e.g., N2); reactive diatomic gases (e.g., O2, Cl2); more complex molecular gases such as CO2 or ammonia (NH3); and organics (e.g., methane (CH4), allylamines, fluorocarbons). Some of the above gases may also be mixed to enhance the effectiveness of the surface treatment.
Gas inlet 70,
Rotary vacuum seals 72a and 72b allow rotation of shaft 62 with respect to proximal and distal fixtures 50a, 50b. It may also be desired to linearly translate catheter manifold 40 within vacuum chamber 10,
Another difficulty in forming plasma in polymer tubing is caused by the presence of an electronically conducting “filler” material in the polymer matrix. The filler (e.g., barium sulfate for radiography) in such “loaded” polymers absorbs energy and attenuates the microwave (or rf) field in the lumen volume, where the plasma is to be generated. Microwave attenuation, when combined with small tubing diameter, produces a serious challenge to plasma generation. The introduction of a fine titanium wire or titanium oxide powder into the tubing lumen has solved these difficulties for ECR plasma generation and maintenance.
It may be desirable to create a “magnetic beach” in vacuum chamber 10,
Highly efficient plasma heating can be achieved with microwaves tuned to the fundamental gyration frequency (AKA, “electron cyclotron frequency”) of free electrons in a magnetic field,
f
v
=f
c=(1/2π)(eB/m) (sec−1) (1)
where B is magnetic field strength, and e and m are charge and mass of the electron (mks units). At this frequency, the electric field of the microwaves are at “resonance” with the gyrating electrons and accelerate them very efficiently. The same principle is employed in high-energy cyclotron particle accelerators. For a magnetic field of 8.75×10−2 Tesla (875 Gauss), the fundamental electron gyrofrequency is 2.45 GHz. In general, when the plasma electron density reaches a high enough level to “cut off” wave propagation at the “plasma frequency,” fp, electromagnetic waves are reflected and plasma heating cannot occur. The plasma frequency, numerically, is given by,
f
p=9(ne)1/2 (sec)−1 (2)
where ne is electron density (m−3). Thus, from equation 2, when plasma density reaches approximately 7.4×1016 m−3, microwaves of a frequency of 2.45 GHz cannot propagate.
An exception to this general rule is for “right-handed” circularly polarized (rhcp) electromagnetic waves 100,
“Whistler” wave propagation has been shown by the referenced authors to be an effective way to introduce microwaves into a dense plasma and for efficient heating of the plasma. The microwaves are initially launched into the vacuum chamber through window 12 (e.g., quartz) that is transparent at the microwave frequency (e.g., 2.45 GHz). Immediately behind the window, there is a “sheath” region 102 in which un-ionized gas and low density plasma is present. Sheath thickness can vary from a few micrometers to a few millimeters, depending on plasma conditions (principally density and temperature). The plasma density quickly increases with distance to a nearly steady-state value, which can be higher than the “critical” value, with plasma frequency higher than given by equation 2.
To heat an overdense plasma with 2.45 GHz microwaves, Stevens et al. used a magnetic field configuration in which rhcp microwaves were launched into a plasma in which the low-density sheath region was permeated with a longitudinal magnetic field whose strength was greater than the “resonance” value (>875 Gauss). In this region, the “whistler” electromagnetic mode could propagate. By means of an electromagnet with specially wound solenoid coils 30,
The inventive ECR plasma system and method allows a reproducible, uniform surface treatment of both flat parts and tubing such as hemodialysis catheters. The latter requires forming ionic plasmas inside the lumen of the small diameter (e.g., 2 mm ID) polymer tubing of the catheter assembly. There are several possible configurations for the catheter processing system, one of which (
Another design employs a vertical cylinder with a multi-arm “cross” at its center (
Uniform surface treatment of external catheter surfaces may require a vacuum-gas feedthrough fixture that physically moves parts within the chamber: both rotational and axial translation. The preferred design is an axially symmetric structure on which more than one catheter or flat part can be mounted. Flat samples or catheters are secured at their upper and lower end and run parallel to the (vertical) axis of the ECR processing chamber. Rotation and translation is incorporated into the design through a planetary gear system that is driven by a central shaft with longitudinal motion capability. Motion control may be accomplished by computer-driven motors.
The fixture for uniform ECR plasma treatment of the interior surface of the catheter tubing includes a manifold 40,
During plasma treatment of catheter lumens, a static gas pressure of a few tens of torr is maintained in the processing vacuum chamber, external to the catheter and fixturing structure. The exterior pressure is high enough (e.g., 200 to 1000 mtorr) to prevent breakdown and plasma formation, which would prevent penetration of the microwaves into the catheter lumens, but low enough to avoid collapse of the catheter walls due to the pressure differential. The pressure differential is established by a gas-handling subsystem 45 and the vacuum subsystem including vacuum port 43 and vacuum pump 41,
In some cases, for example catheters constructed of polymer that is “loaded” with a radio-opaque substance such as barium sulfate, it may be difficult to initiate a plasma in the lumen because the “loading” partially absorbs microwave energy. For such cases, it may be necessary to insert material into the lumen to “trigger” plasma formation. One approach is to insert a fine (e.g., 0.1 mm diameter) metal wire 80, such as Ti, Pt, Ag, etc.
As shown in
Monitoring of the plasma is accomplished by plasma emission (PE) spectroscopy, in which the spectrum and intensity of characteristic emission lines are monitored through a window in the processing chamber. The presence, absence, or relative intensity of certain emission lines are sensitive indicators of desired (or anomalous) conditions in the plasma. Additionally, the intensity and time variation of spectrally integrated light emission from the plasma, measured by photodiodes on chamber windows, provide electrical signals that reflect plasma homogeneity, temperature and density, and stability.
In
In
Table 1 lists the type and dimensions of samples employed during testing.
Tubing samples of approximately 20 cm length were mounted inside a vacuum chamber. The samples were suspended vertically in the center of the chamber and placed so that they were exposed to the plasma in the central ECR zone. The chamber was evacuated to less than 30 mTorr and gas was flowed for 45 minutes or more, under the pressure (70 to 150 mTorr) at which the plasma treatment was to be performed. The low pressure and period of active gas flow removed adsorbed water vapor and residual isopropyl alcohol used for cleaning the exterior tubing surface. The 2.45 GHz microwave supply was then applied at a pre-set power level (usually 100 W), upon which plasma immediately formed. At the end of the process time (0.5 to 15 minutes), microwave power was removed, the vacuum valve closed, and air was admitted into the chamber. The samples were then immediately removed for analysis.
The plasmas were formed in high purity (99.999%) nitrogen, argon, and 50% mixtures of argon and oxygen or nitrogen and oxygen. An oxidizing plasma environment has been shown to produce considerably different surface chemistry on silicone than plasmas of inert or reducing gases such as argon, nitrogen, or ammonia, where the latter tend to create functional silicon-hydride (Si—H) groups onto which bioactive molecules can be bonded. The presence of oxygen in the plasma, on the other hand, causes surface oxidation and the formation of relatively stable C═O groups.
Tubing samples of approximately 40 cm length were mounted inside a vacuum chamber. The tubing lumen was evacuated to less than 30 mTorr and gas was flowed through the tubing for 60 minutes or more, under the pressure (70 to 150 mTorr) at which the plasma treatment was to be performed. The 2.45 GHz microwave supply was then applied at a pre-set power level (usually 100 W) and plasma formed in the tubing. The process time (10 to 120 seconds) was considerably shorter than for exterior treatments, because the plasma was very intense in the small diameter lumen and discolored the polymer if the process was continued for too long a period. After processing, the microwave power was removed, the vacuum valve closed, and air was admitted into the tubing lumen. The samples were then immediately removed for analysis.
The tubing wall was rigid enough to support fill atmospheric pressure; thinner wall tubing would be processed with a partial pressure that is high enough to prevent external breakdown (preventing plasma formation in the lumen) but low enough to avoid collapse of the tubing wall (e.g., 0.2-1 Torr).
Flat sheets of silicone rubber and polyurethane with composition and properties nearly identical to those of the tubing samples were cut into rectangles approximately 2 by 3 cm and suspended in the vacuum chamber by thin strips of the same material. Their placement near the center of the chamber closely resembled that of the tubing samples when treated on their external surface. Procedures for evacuation, gas flow, and plasma treatment were identical to those for the tubing samples that were processed externally.
Tubing exteriors and flat-sample surfaces were evaluated with a goniometer (Kernco, El Paso, Tex.), which is equipped with a movable stage and microscope to measure the tangent angle between small droplets of water and the surface under study. Several contact-angle measurements are averaged to determine the wettability of a given surface. In general, a surface with water contact-angle between 0° and 90° is considered hydrophilic, whereas surfaces with contact angles greater than 90° are considered hydrophobic. Quantitative measurements of surface energy (units: J/m2 or dyne/cm) must be performed with a series of different liquids, each with a different intrinsic surface tension; a plot of contact-angle vs. liquid surface tension (at constant temperature) leads to a value of “critical” surface energy that is characteristic of the surface under evaluation. A surface whose critical energy is greater than 71.9 dyne/cm (7.19×10−2 J/m2) is completely wettable by water (contact angle of 0°). Tabulated critical energy values of clean silicone rubber and polyurethane surfaces are respectively ca. 24 dyne/cm and 35 dyne/cm. Thus, they should have a water contact-angle >0°. As shown below, untreated surfaces of both polymers show water contact-angles near 90°.
A series of experiments was performed to investigate surface energy of ECR plasma-treated polymer tubing through water contact-angle measurements. First, the effect of plasma exposure duration was studied on silicone rubber tubing samples of 6.7 mm OD.
Silicone tubing samples were stored in room air, and water contact-angles were measured as a function of time after ECR plasma processing.
The rise of a liquid in a capillary can be related to surface energy through the equation,
where μ(dyne/cm) is the difference between surface energy and surface tension of the liquid (dyne/cm), θ is the contact-angle between the liquid and surface, ρ is liquid density (g cm−3), g is the acceleration of gravity (981 cm s−2), and r is the radius of the capillary (cm). In actual practice, contact-angle θ is nearly impossible to measure accurately, so the cosine term is assumed to be close to unity, a reasonable assumption when h>r. When the rise is small or negative compared to the external liquid level, equation 3 only gives a comparative value for the material's surface energy.
The lumen of silicone rubber tubing of two different diameters (see Table 1) was successfully treated with ECR plasma. Surface activation in the lumen was shown by a dramatic rise in the level of deionized water in the treated samples: after plasma treatment, water in the lumen changed from a convex meniscus below the external water level to a concave meniscus that was well above. Table 2 summarizes data on interior surface treatment of silicone rubber tubing. All plasma treatments produced approximately the same change of surface energy, from hydrophobic to hydrophilic. A control length of silicone tubing that was handled exactly like that of the ECR plasma-treated samples, except without exposure to plasma, showed the same low surface energy as virgin controls.
The rise of water level by capillary action remained at nearly the same height in plasma-treated silicone samples as long as they were stored in water. Treated samples exposed to room air lost their strong hydrophilicity over a period of 2 to 3 days, although never became as hydrophobic as untreated controls.
Table 3 summarizes experimental conditions for exterior surfaces of polyurethane tubing samples and water contact-angle data immediately after ECR plasma treatment. All plasma gases produced significant reduction of water contact angle on polyurethane tubing, with argon plasma giving the lowest angles.
Surface activation in the lumen of polyurethane tubing was shown by a dramatic change of the level of deionized water in the treated samples. After plasma treatment, water in the lumen changed from a convex meniscus below the external water level to a concave meniscus that was well above. Table 4 summarizes data on interior surface treatment of polyurethane tubing with 3.3 mm OD and 2.7 mm ID. All plasma treatments produced approximately the same change of surface energy, from hydrophobic to hydrophilic. A control length of polyurethane tubing that was handled exactly like that of the ECR plasma-treated samples, except without exposure to plasma, showed the same low surface energy as virgin controls.
The water level remained at the same height in plasma-treated polyurethane samples as long as they were stored in water. Treated samples exposed to room air lost their strong hydrophilicity over a period of 2 to 3 weeks, although never became as hydrophobic as untreated controls. In general, plasma-treated polyurethane remained hydrophilic considerably longer than silicone rubber under exposure to air.
A polyurethane tubing sample that underwent a 20 sec. argon plasma treatment along with an untreated control was placed in a vessel of toludine-blue dye diluted in water. The dye level in the plasma-treated tubing was about 9 mm above the surface of the liquid and about 12 mm above the meniscus in the untreated tubing. This is a graphic demonstration of the strong capillary effect produced by ECR plasma treatment.
A demonstration was performed on silicone rubber tubing that is nearly identical to that of a hemodialysis catheter. The plasma treatment allowed for the grafting of a monomer-protein coating to the silicone rubber by functionalizing and activating the surface of the silicone polymer.
A 40 cm length of tubing with 5.3 mm OD and 3.3 mm ID (see Table 1) was configured for plasma treatment inside its lumen, and an argon plasma generated in a segment approximately 6 cm in length. Immediately following extinction of the ECR plasma and while still under vacuum, the activated surface of the lumen was exposed to glycidyl methacrylate to form a thin coating on the lumen wall. Upon removal of the silicone tubing from the apparatus, the coated segment was heated to 80° C. for 30 min. to further polymerize the monomer, and then soaked in an albumin solution (0.3 mg/mL) for 18 hrs. For comparison, a control sample of tubing, not treated with argon plasma or monomer, was soaked in albumin.
A visual test determined the presence of the monomer-albumin coating on the plasma-treated tubing versus the untreated control soaked in albumin. The ECR plasma-treated tubing had a translucent appearance, whereas the control was completely transparent, indicating lack of adsorption of the protein. The albumin was bound covalently to the monomer in this experiment and this result can be extrapolated to the application of a heparin-containing or another bioactive substance, in order to achieve a surface with antithrombotic characteristics. The attachment of glycidyl methacrylate and albumin to normally hydrophobic silicone rubber is a proof-of-concept for attaching other bioactive molecules to polymer surfaces. The experiment shows that other gases or low boiling-point liquids, such as NH3, allylamines, fluorocompounds, and unsaturated hydrocarbons, can also be used for surface activation and functionalization.
In accordance with the subject invention, the right-hand circularly polarized microwaves along a longitudinal magnetic field provide more efficient coupling of the microwave power to initiate and maintain a plasma than with linearly polarized waves. The magnetic beach discussed herein is a further improvement of microwave-plasma coupling. Another feature of the subject invention is the integrated processing chamber and solenoid magnet. Vertical orientation of the processing chamber in a solenoid magnet assists in processing long, thin tubing or catheters. Plasma processing with a differential coupling system as described herein allows treating the inside and the outside of the tubing with different gas plasmas or processed conditions without the need to remove the articles from the chamber or break the vacuum. The use of a “Penning” gas mixture (for example, helium with traces of argon) in a plasma reduces the gas breakdown threshold and aids in initiation and maintenance of a plasma inside very small diameter tubings and/or polymer tubing with conductive “fillers” (for example, barium sulfate). The insertion of the fine metal wire such as Ti along the axis of the very small diameter tubing and/or a polymer tubing with conductive fillers also aids in the initiation of the plasma. Similar results can be obtained by the insertion of a titanium powder on the inside walls of the catheter or tubing. Rotating and/or translating the catheter (including the inserted metal wire) and/or with respect to the processing chamber ensures a uniform surface treatment by the plasma.
One method of pretreating the lumen of a polymer catheter for grafting with a bioactive material in accordance with the subject invention includes generating circularly polarized microwaves at a frequency which produces electron cyclotron resonance and propagating the microwaves to a plasma zone. A magnetic field is produced in the plasma zone with magnetic field lines co-linear with the propagation direction of the microwaves. The polymer catheter is subject to the plasma zone and a gas is introduced in the lumen thereof generating plasma in the lumen which pretreats the same. The system of
The method may further include pretreating the outer surface of the polymer catheter. After treatment, the pretreated polymer catheter can be coated with a bioactive material (e.g., an anti-microbial material, or an anti-thrombogenic material). Exemplary anti-microbial materials include selenium, silver, penicillin, tetracycline, sulfa drugs, quaternary ammonium compounds, and/or octenidine dihydrochloride. Exemplary anti-thrombogenic materials include heparin, antithrombin-III—heparin (ATH), collagen, poly hexamethylene biguanide hydrochloride, adenosine diphosphatase (ADPase), tissue factor pathway inhibitor (TFPI), nitric oxide, polyethylene oxide, thrombomodulin, pentasaccharide, hirulog, hirudin, PPACK, phosphoral chlorine and/or tetra ethylene glycol ether (tetraglyme). The method may further include the step of coating the pretreated polymer catheter with a monomer base layer for coupling with a bioactive material. Examples of monomer base layer includes glycidyl methacrylate, acrylic acid, acrylamide, allyl alcohol, allyl amine, and/or modified albumin. The method may further include the step of pretreating the catheter with a monomer base layer for coupling with a hydrophilic material such as polyethylene glycol, hyaluronic acid, polysaccharides, polyvinyl alcohol, polyisopropyl acrylamide, polyvinylpyrrolidinone, star polymers and/or dendrimers based on the above. The method may further include the step of pretreating the catheter with a monomer base layer for coupling with a hydrophobic material such as fluorocarbons, saturated hydrocarbons, and their self-assembled monolayers.
Catheters which can be pretreated in accordance with the subject invention include catheters fabricated of polyurethane, silicone rubber, polyethylene, polypropylene, and fluorinated hydrocarbons such as PTFE and Teflon. Preferred polymeric substrates to be treated may include a variety of natural or synthetic polymers. The types of polymers include but not limited to: polyolefins, silicones, acrylic polymers, vinyl halide polymers, polyhydroxyalkanoates (PHAs), polyvinyl ethers, polyvinyl aromatics, polyamides, polyesters, resins, polyurethane, polyimides, polyethers, natural or synthetic rubbers, natural polymers such as wool, cotton, silk, and copolymers consisting two or more polymeric components mentioned above. Examples include but not limited to: acrylonitrile-styrene copolymers, polyacrylate, polyacrylonitrile, polyethylene, polypropylene, polyisobutylene, polydimethylsiloxane, polyetheretherketone (PEEK), polyethersulphone, polymethylmethacrylate, polyethylacrylate, polyvinyl chloride, polytetrafluoroethylene, chlorotrifluoroethylene, fluorinated ethylene-propylene, polyvinylidene fluoride, ethylene tetrafluoroethylene copolymer, perfluoropolyethylene, ethylene propylene copolymer, polyvinyl methyl ether, polyvinylidene fluoride, polyvinylidine chloride, polystyrene, polyvinyl acetate, ethylene-methylmethacrylate copolymers, ABS resins, ethylene-vinyl acetate copolymers, butadiene-styrene copolymers, polyisoprene, synthetic polyisoprene, polybutadiene, butadiene-acrylonitrile copolymers, polychloroprene rubbers, polyisobutylene rubber, ethylene-propylenediene rubber, isobutylene-isoprene copolymers, polyurethane rubber, nylon 66, polycaprolactam, polyethylene teraphthalate, polylactide, polycaprolactone, polyglycolide, polylactide-co-glycolide, polyhydroxybutyrate, phenol-formaldehyde resins, polycarbonates, polyoxymethylenes, polyimides, polyethers, epoxy resins, polyurethanes, wool, cotton, silk, rayon, rayon-triacetate, cellulose acetate, cellulose butyrate, cellulose acetate butyrate, cellulose nitrate, cellulose propionate, cellulose ethers, carboxymethyl cellulose, polyether block amides, polycarbonates, polyvinyl pyrrolidinones, polyvinyl alcohols, styrene acrylonitrile, and composites made from one or more of the above-mentioned polymers and/or fibers or additives. A preferred group of polymers include those of polyurethane, polyolefin, silicone, fluoropolymer, polyester, polyvinyl halide, polyether, polyamide, and blends/copolymers thereof.
A typical processing sequence includes loading one or more previously cleaned tubing segments or catheters onto the processing fixture. The tubing may have a fine metal wire on axis or titanium oxide powder on interior (lumen) walls. Each end of the individual tubes is sealed to the vacuum couplings (“quick disconnects”) on the fixture. The loaded fixture is introduced on the axis of the processing chamber, vacuum-sealed to the chamber, and gas-delivery, vacuum piping, and electrical connections for mechanical movement motors are then attached to feed-through ports in fixture's main vacuum flange.
Air and residual gases are then pumped from the processing chamber, tubing lumens, and all associated piping, gas-handling, gas-distribution, and gas-mixing apparatus.
Process gas(es) for treatment of the lumen wall is flowed at appropriate pressure (1-5×10−2 Torr) via the processing fixture. Pure gas (e.g., Ar, N2) is flowed into the processing chamber until a pressure level is reached that will prevent plasma formation external to the tubing lumen (e.g., 0.2 to 1 Torr).
Mechanical rotation or angular oscillation of the processing fixture and/or individual tubing articles is initiated. Longitudinal movement or linear oscillation is initiated, if required. Then the magnetic field is applied at appropriate level. Microwave power is applied at appropriate level for a predetermined processing time. Visual observation and automated diagnostics assure good plasma properties and uniformity. After treatment, microwave power, magnetic field, mechanical movement, and gas flow are turned off.
Following treatment of the tubing lumens, the external walls are treated. The gas previously introduced is pumped from the processing chamber, and a flow of treatment gas(es) is initiated through the chamber, following adjustment to the desired gas species and pressure. Then a plasma is formed in the processing chamber treating the external walls of the tubing. After treatment, gas-delivery and vacuum piping and electrical connections are disconnected from feed-through ports on the main vacuum flange of the fixture. The processing fixture is removed from the chamber and the tubing is unloaded from the fixture. Quality control and inspection of treated articles is performed. Finally, a monomer or polymer attachment layer and/or bioactive coating is applied to the treated articles. The catheter manifold, fittings, and other fixtures may be fabricated of a non-electrically conductive material, such as a high-temperature plastic such as Teflon or Delrin.
Although specific features of the invention are shown in some drawings and not in others, this is for convenience only as each feature may be combined with any or all of the other features in accordance with the invention. The words “including”, “comprising”, “having”, and “with” as used herein are to be interpreted broadly and comprehensively and are not limited to any physical interconnection. Moreover, any embodiments disclosed in the subject application are not to be taken as the only possible embodiments.
In addition, any amendment presented during the prosecution of the patent application for this patent is not a disclaimer of any claim element presented in the application as filed: those skilled in the art cannot reasonably be expected to draft a claim that would literally encompass all possible equivalents, many equivalents will be unforeseeable at the time of the amendment and are beyond a fair interpretation of what is to be surrendered (if anything), the rationale underlying the amendment may bear no more than a tangential relation to many equivalents, and/or there are many other reasons the applicant can not be expected to describe certain insubstantial substitutes for any claim element amended.
Other embodiments will occur to those skilled in the art and are within the following claims.
