Medical tubing and forming method

Abstract

In one embodiment, a medical tubing (10) having a clear or transparent appearance adapted for in vivo transport of aqueous fluids to a subject and which is manually bendable, comprising an inner layer (3), a middle layer (2) and an outer layer (1), wherein the inner layer (3) comprises polypropylene, the outer layer (1) comprises a thermoplastic polyurethane or a cyclic olefin copolymer, and the middle layer (2) is selected from one or more of ethylene vinyl acetate copolymer, ethylene acrylate copolymer, ethylene-acrylate maleic anhydride terpolymer, ethylene-acrylate glycidyl methacrylate terpolymer, and maleic anhydride grafted polypropylene.

Description

Technical Field

[0001]

[0001] The present invention relates to polymeric tubing for delivering a medical fluid to a patient and to a method of forming such tubing having multiple layers of the same or different polymeric materials, each layer adhesively bonded in succession to the others, which is typically carried out by a coextrusion process.

Background Art

[0002]

[0002] Tubing made of polymeric materials is used in many industrial and commercial applications, including the medical field. A variety of FDA-compliant plastic products are used depending on the desired properties and intended use. The selection of the polymeric material can be a factor when tubing is used to transport fluids for in vivo treatment of human patients.

[0003]

[0003] A three-layer tubing using a polyethylene-based polymer as the innermost layer in contact with a medical fluid has been used, and this innermost polyethylene layer is joined to the outermost layer of polyurethane through a central or intermediate layer of an adhesive as disclosed in U.S. Patent No. 10,646,704. Such tubing structures have several advantages, but the polyethylene tubing layer in contact with typical aqueous fluids for medical procedures may have a negative interaction with certain commonly useful medical fluids such as aqueous compositions of insulin and other drugs.

[0004]

[0004] Polyvinyl chloride (PVC) is one of the most widely used plastic products. While structurally stable and easily molded into desired shapes, PVC is typically manufactured using plasticizers that have other properties that make it unsuitable for medical treatment applications, such as the ability to migrate from the PVC matrix into bodily fluids. Similarly, due to the inherent properties of plasticized PVC tubing, there is a possibility that drugs and other components of aqueous fluids used in medical treatments may be absorbed into the sidewalls of the PVC tube. Polyurethane is a potentially suitable substitute for PVC. However, two-layer tubing composed of polyurethane and polyethylene cannot retain its bond to one another under low to moderate stress, strain, or mechanical operating conditions. U.S. Patent No. 4,627,844 of Schmitt, incorporated herein by reference as if its disclosure were contained in whole, discloses a three-layer tubing embodied in a commercial product sold under the trademark “SUREPATH 151” by the Natvar Division of Tekni-Plex, Inc. As disclosed in Schmitt, the outer layer of PVC and the inner layer of low-density polyethylene (LDPE) that comes into contact with the fluid are co-extruded together with an intermediate layer of ethylene vinyl acetate copolymer (EVA) binder. However, while the inner polyethylene layer in Schmitt may be inert to or not interfere with some components of medical fluids, polyethylene may interact inversely with other components of medical fluids, such as many common fluid compositions containing insulin. [Overview of the project] [Problems that the invention aims to solve]

[0005]

[0005] As described above, pipe materials with a polyethylene inner layer may have negative interactions with pharmaceutical components over a long period of time.

[0006] According to the present invention, the selection of polypropylene as the inner polymer material can prevent unwanted loss of components / absorption of pharmaceutical components and can protect the integrity of formulations in normal use in tubing materials that deliver aqueous fluids such as drug suspensions, chemotherapeutic drugs, and insulin to or from human subjects.

[0006]

[0007] In a two-layer pipe consisting of an inner polypropylene layer and an outer polyurethane layer, the two layers cannot remain bonded to each other.

[0008] The present invention relates to an intermediate layer that connects the inner and outer layers together and prevents delamination of the multilayer structure under moderate stress, strain, or mechanical operation. [Means for solving the problem]

[0007]

[0009] The selection of an appropriate intermediate polymer material prevents delamination of the multilayer structure, protecting the bonding of tubing, tubing and fittings, and the integrity of the delivered formulation.

[0010] The polymer material for the intermediate layer is selected from one or more of the following: ethylene vinyl acetate copolymer, ethylene acrylate copolymer, ethylene-acrylate maleic anhydride terpolymer, ethylene-acrylate glycidyl methacrylate terpolymer, and maleic anhydride grafted polypropylene.

[0008]

[0011] Thermoplastic polyurethane as an outer layer is beneficial for medical tubing where PVC is undesirable due to the presence of plasticizers. TPU provides secure bonding to fixtures during post-tube manufacturing and assembly of medical devices. Alternatively, the TPU outer layer can be replaced with a cyclic olefin copolymer to provide desired performance characteristics at a lower cost.

[0009]

[0012] A tube (10) adapted for in vivo transport of an aqueous fluid to a target, comprising an inner layer (3), an intermediate layer (2), and an outer layer (1) in one embodiment of the present invention, Formed by a co-extrusion process, the inner layer (3), intermediate layer (2), and outer layer (1) are concentric, and the inner layer (3) and outer layer (1) are bonded to the intermediate layer (2), and are bonded to each other by being bonded to the intermediate layer (2). The inner layer (3) contains polypropylene. The outer layer (1) contains thermoplastic polyurethane, The intermediate layer (2) is selected from one or more of ethylene vinyl acetate copolymer, ethylene acrylate copolymer, ethylene-acrylate maleic anhydride terpolymer, ethylene-acrylate glycidyl methacrylate terpolymer, and maleic anhydride grafted polypropylene, in the tube.

[0010]

[0013] In one embodiment of the present invention, the intermediate layer (2) comprises an ethylene ethyl acrylate copolymer, an ethylene methyl acrylate copolymer, an anhydride-grafted ethylene methyl acrylate copolymer, two or more copolymers of the acrylate, or a mixture of two or more of the above.

[0011]

[0014] In one embodiment of the present invention, the intermediate layer (2) comprises ethylene vinyl acetate.

[0015] In one embodiment of the present invention, the inner layer (3) comprises more than 90% by weight of a polypropylene homopolymer or polypropylene copolymer, the outer layer (1) comprises more than 90% by weight of an aromatic or aliphatic polyether polyurethane, and the intermediate layer (2) comprises more than 90% by weight of one or more of ethylene vinyl acetate copolymer, ethylene acrylate copolymer, ethylene-acrylate maleic anhydride terpolymer, ethylene-acrylate glycidyl methacrylate terpolymer, and maleic anhydride grafted polypropylene.

[0012]

[0016] In one embodiment of the present invention, the intermediate layer (2) comprises an ethylene ethyl acrylate copolymer having an ethyl acrylate content of at least 19.5 percent by weight.

[0017] In one embodiment of the present invention, the intermediate layer (2) contains more than 90% by weight of ethylene methyl acrylate copolymer.

[0013]

[0018] In one embodiment of the present invention, the intermediate layer (2) contains ethylene vinyl acetate with a vinyl acetate content of at least 19.5 percent by weight.

[0019] In one embodiment of the present invention, the inner layer (3) comprises more than 90% by weight of a polypropylene homopolymer or polypropylene copolymer or a mixture of homopolymer and copolymer, and the outer layer (1) comprises more than 90% by weight of a polytetramethylene glycol-based polyurethane.

[0014]

[0020] In one embodiment of the present invention, the thickness of the polyurethane outer layer is 0.0254 to 0.635 mm (0.001 to 0.025 inches), the thickness of the inner polypropylene layer is 0.0254 to 0.635 mm (0.001 to 0.025 inches), and the thickness of the intermediate layer is 0.0254 to 0.635 mm (0.001 to 0.025 inches).

[0015]

[0021] In one embodiment of the present invention, the inner layer (3) and outer layer (1) do not visually delaminate from the intermediate layer (2) under stresses of 20 MPa or less and strains of 400% or less.

[0022] In one embodiment of the present invention, the tube (10) does not visually delaminate when immersed in water at 60°C for 72 hours.

[0016]

[0023] In one embodiment of the present invention, the tube (10) has a central axial fluid channel, which is a path for an aqueous fluid to pass through, the inner layer (3) has radially inwardly facing walls in contact with the aqueous fluid, the outer (1) and inner (3) layers resist delamination from the intermediate layer (2) with stresses of 20 MPa or less and strains of 400% or less, and the tube (10) does not visually delaminate after being immersed in water at 60°C for 72 hours.

[0017]

[0024] In one embodiment of the present invention, the inner layer (3) and the outer layer (1) do not visually delaminate from the intermediate layer (2) under a stress of 20 MPa or less and a strain of 400% or less, and the tube (10) does not visually delaminate after being immersed in water at 60 °C for 72 hours.

[0018]

[0025] In one embodiment of the present invention, the outer layer (1) contains more than 90% by weight of an aromatic polyether-based polyurethane, and the tube does not visually delaminate after being immersed in water at 60 °C for 72 hours.

[0019]

[0026] A method for delivering an aqueous fluid in vivo in one embodiment of the present invention, comprising: selecting one or more aqueous compositions effective for treating the condition of a subject, the aqueous composition being selected from the group consisting of an aqueous drug suspension, an aqueous composition containing a chemotherapeutic agent, and an aqueous composition containing insulin; delivering the one or more selected aqueous compositions to the subject through a flow through the tube via the tube; The method comprising.

[0020]

[0027] A method of forming a medical tube that is transparent or has a clear appearance and is manually bendable for in vivo transport of an aqueous fluid in one embodiment of the present invention, comprising: selecting a first polymer material that is an aromatic or aliphatic polyether-based polyurethane material having a specific structural stability; selecting a second polymer material that is a polypropylene material inert to the aqueous fluid; selecting a third polymer material having elastomeric properties, having visual clarity, and being selected from one or more of ethylene vinyl acetate copolymer, ethylene acrylate copolymer, ethylene-acrylate maleic anhydride terpolymer, ethylene-acrylate glycidyl methacrylate terpolymer, and maleic anhydride grafted polypropylene; Coextruding the selected first, second, and third polymer materials to form the adhered outer layer, inner layer, and intermediate layer of the medical tube, with the outer layer containing at least 90% by weight of the first polymer material, the inner layer containing at least 90% by weight of the second polymer material, and the intermediate layer containing at least 90% by weight of the third polymer material including The materials are selected to maintain the integrity of the tube against delamination and maintain its clear or transparent appearance after being subjected to one or more of ethylene oxide and gamma-ray irradiation sterilization. The medical tube has a central axial fluid flow path defined by the radially inward wall surface of the inner layer, the central axial fluid flow path transports an aqueous fluid, the tube is immersed in water at 60 °C for 72 hours, and then is mechanically flattened by being manually crushed from its normal round cross-sectional state to a crushed or oval cross-sectional shape or state, and does not visually delaminate.

[0021]

[0028] A tube (10) including an inner layer (3), an intermediate layer (2), and an outer layer (1) in one embodiment of the present invention, suitable for in vivo transport of an aqueous fluid to a subject, Formed by a coextrusion process, the inner layer (3), the intermediate layer (2), and the outer layer (1) are concentric, the inner layer (3) and the outer layer (1) are adhered to the intermediate layer (2), and are adhered to each other by being adhered to the intermediate layer (2). The inner layer (3) contains polypropylene. The outer layer (1) contains a cyclic olefin copolymer. The intermediate layer (2) is selected from one or more of ethylene vinyl acetate copolymer, ethylene acrylate copolymer, ethylene-acrylate maleic anhydride terpolymer, ethylene-acrylate glycidyl methacrylate terpolymer, and maleic anhydride grafted polypropylene.

[0022]

[0029] In one embodiment of the present invention, the inner layer (3) comprises more than 90% by weight of a polypropylene homopolymer or polypropylene copolymer, the outer layer (1) comprises more than 90% by weight of a cyclic olefin copolymer, and the intermediate layer (2) comprises more than 90% by weight of one or more of ethylene vinyl acetate copolymer, ethylene acrylate copolymer, ethylene-acrylate maleic anhydride terpolymer, ethylene-acrylate glycidyl methacrylate terpolymer, and maleic anhydride grafted polypropylene.

[0023]

[0030] In one embodiment of the present invention, the inner layer (3) and outer layer (1) do not visually delaminate from the intermediate layer (2) under stresses of 20 MPa or less and strains of 400% or less, and the tube (10) does not visually delaminate after being immersed in water at 60°C for 72 hours.

[0024]

[0031] In one embodiment of the present invention, a method for delivering an aqueous fluid in vivo: The step of selecting one or more aqueous compositions effective for treating the target condition, wherein the aqueous composition is selected from the group consisting of aqueous drug suspensions, aqueous compositions containing chemotherapeutic agents, and aqueous compositions containing insulin. The steps include delivering one or more selected aqueous compositions to a target through a tube via a flow through the tube, Methods that include...

[0025]

[0032] A method for forming a transparent or clear-looking, and manually bendable medical tube for in vivo transport of an aqueous fluid, according to one embodiment of the present invention, The steps include selecting a first polymer material which is an aromatic or aliphatic polyether-based polyurethane material having specific structural stability; The steps include selecting a second polymer material, which is a polypropylene material that is inert to aqueous fluids; The steps include selecting a third polymer material having elastomer properties and visual clarity, comprising an acrylate copolymer selected from one or more of ethylene vinyl acetate copolymer, ethylene acrylate copolymer, ethylene-acrylate maleic anhydride terpolymer, ethylene-acrylate methacrylate glycidyl terpolymer, and maleic anhydride grafted polypropylene, The steps include co-extruding selected first, second, and third polymer materials to form bonded outer, inner, and intermediate layers of a medical tube, wherein the outer layer contains at least 90% by weight of the first polymer material, the inner layer contains at least 90% by weight of the second polymer material, and the intermediate layer contains at least 90% by weight of the third polymer material. Includes, The material is selected to maintain the integrity of the tube against delamination and its clear or transparent appearance after being subjected to one or more ethylene oxide and gamma irradiation sterilization. A medical tube has a central axial fluid channel defined by radially inward-facing walls in the inner layer, the central axial fluid channel transports aqueous fluid, and the tube does not visually delaminate after being immersed in water at 60°C for 72 hours, and subsequently mechanically flattened by manually crushing it from its normal round cross-sectional state to an oval cross-sectional shape or state.

[0026]

[0033] The drawings depict one or more embodiments of the present invention as shown in the examples of the present invention. [Brief explanation of the drawing]

[0027] [Figure 1]

[0034] Figure 1 is a schematic perspective view of a three-layer tube showing the outer and middle layers, fractured to better illustrate the structure and arrangement of the tubing; [Figure 2]

[0035] Figure 2 is a cross-sectional view taken along line 2-2 of tube 10 shown in Figure 1. [Figure 3]

[0036] Figure 3 is a photograph of a cross-section of a tube having an inner layer, intermediate layer, and outer layer subjected to tensile testing using a Lloyd tensile testing machine. The three-layer tube is subjected to high tension pulling or stretching to determine whether one layer is pulled past the other under the applied high tension, thus indicating the relative degree of adhesion of the intermediate layer to the inner and outer layers. [Figure 4]

[0037] Figure 4 is a matrix or chart showing the layer thickness and composition of one embodiment (SR#2597), a comparative 2M2L embodiment (SR#2604), and two further embodiments (SR#2605 and SR#2606) of a 3M3L tube having an EMAC intermediate layer according to the present invention. [Figure 5]

[0038] Figure 5 is a side view of two sample tubes, namely the 3M3L SR#2597 according to the present invention on the left and the comparative 2M2L on the right, visually demonstrating the layer separation. Each tube was measured microscopically (L, unit 0.0254 mm = 1 mil (n=5)) after being sandwiched and rotated 10 times and then aged for 3 days in distilled water at 60 degrees Celsius. Here, the sample of the present invention on the left had an L value of 0.11049 mm (4.350 mil), while the comparative tube on the right had a much larger L value of 1.3120624 mm (51.656 mil) (only greater layer separation compared to the 2M2L tube). [Figure 6]

[0039] Figure 6 is a matrix or chart showing side-microscope measurements (L, unit 0.0254 mm = 1 mil), similar to Figure 4, listing five samples for each of SR#2597 (invention, 3M3L, with EMAC interlayer), SR#2604 (2M2L, comparison), and Sr#2605 and SR#2606 (invention, 3M3L, with EVA interlayer), with the average L value listed for each group of the five samples, again showing that the 3M3L samples have much lower layer separation L values ​​than the 2M2L samples. [Figure 7]

[0040] Figure 7 is a 200X microscope cross-sectional view of two sample tubes, 3M3L SR#2597 according to the present invention on the left and comparative 2M2L SR#2604 on the right, visually showing the stratification along with the visual evaluation grade (grade 1-5) for each tube after being sandwiched and rotated 10 times and then aged for 3 days in distilled water at 60 degrees Celsius, where the sample of the present invention on the left had a grade of 2.5, and the comparative tube on the right had a much higher grade value of 4.75 (lower values ​​are desirable). [Figure 8]

[0041] Figure 8 is a matrix or chart showing the visual evaluation grade of the cross-section, as in Figure 6, listing five samples for each of SR#2597 (invention, 3M3L, with EMAC interlayer), SR#2604 (2M2L, comparison), and Sr#2605 and SR#2606 (invention, 3M3L, with EVA interlayer), and listing the average grade value for each group of the five samples, again showing that the 3M3L samples have a much lower layer separation L value than the 2M2L samples. [Figure 9]

[0042] Figure 9 is a graph showing tensile curves for one 2M2L (SR#2604) and various 3M3L tubes, each with a different intermediate layer (EMAC SR#2597, EVA SR#2605, and EVA SR#2606), where the tubes were set up for insulin delivery, with stress (psi) on the vertical axis and strain (%) on the horizontal axis. Here, all 3M3L tubes showed much lower layer separation (also known as sleeving) than the 2M2L samples. [Figure 10]

[0043] Figure 10 is a matrix or chart showing various tensile properties for the 3M3L tubes with different intermediate layers (EMAC SR#2597, EVA SR#2605, and EVA SR#2606) within the various tubes shown in Figure 8, namely 2M2L (SR#2604) and 3M3L tubes. All 3M3L tubes showed much better tensile properties and lower layer separation (also known as sleeving) than the 2M2L samples. [Modes for carrying out the invention]

[0028]

[0044] Figure 1 shows one embodiment of a co-extruded three-layer tubing 10 according to the present invention, comprising an outer layer 1 composed of at least about 90 wt% polyurethane material, typically a polytetramethylene glycol-based polyurethane, one example being Lubrizol TPU Pellethane 2363-90AE. The outer layer may instead contain a cyclic olefin copolymer material such as Topas E-140.

[0029]

[0045] As shown in Figure 1, the tube typically comprises an inner fluid-contacting layer 3 composed of at least about 90 wt% of a polypropylene material such as Ineos R01C, and an intermediate bonding layer 2 composed of at least about 90 wt% of ethylene ethyl acrylate copolymer, ethylene methyl acrylate copolymer, anhydride-grafted ethylene methyl acrylate copolymer, two or more copolymers of the acrylates, or a mixture of two or more acrylate compounds or compositions. One example of a suitable ethylene ethyl acrylate copolymer is Dow Amplify EA 103 (ethylene ethyl acrylate is about 19.5 wt%). Examples of suitable ethylene methyl acrylate copolymers are Westlake MA SP2268 (ethylene methyl acrylate is about 24 wt%) and Westlake MA SP2220 (ethylene methyl acrylate is about 20 wt%). One example of a suitable anhydride-grafted ethylene methyl acrylate copolymer is Westlake Tymax GA 7001 (anhydride-grafted ethylene methyl acrylate). The intermediate layer can instead contain an ethylene-vinyl acetate copolymer.

[0030]

[0046] As shown in Figure 1, the outer layer 1 has a radially inward surface S1 that bonds to and adheres to a radially outward surface S2 of the intermediate layer 2. Similarly, the inner layer 3 has a radially outward surface S4 that bonds to and adheres to a radially inward surface S3 of the intermediate layer 2. The intermediate layer 2 is bonded to the outer layer 1 and the inner layer 3, and layers 1 and 3 remain bonded to layers 2 and to each other when the length of a tube 10 with an axial length L of approximately 5.08 cm (2 inches) is pulled along its axis A, as measured by using a Lloyd LR5K Plus mechanical testing machine at a tensile speed of approximately 30.48 cm (12 inches) / min, ambient environmental conditions of approximately 22.22°C (72°F) and approximately 50% relative humidity. The tube 10 remains bonded to layers 2 and to each other when subjected to a stress of approximately 20 MPa or less and a strain of approximately 400%, where the fracture point of the tube 10 is approximately 17-22 MPa and approximately 300-450%. The layers 1, 2, and 3 of the pipe material 10 are subjected to immersion in water at 60°C for 36 or 72 hours, and subsequently mechanically flattened by being manually crushed from their normal round cross-sectional state to a flattened or oval cross-sectional shape or state, after which they do not visually delaminate.

[0031]

[0047] As shown in Figures 1 and 2, layers 1, 2, and 3 form structurally stable walls that surround and enclose the central hollow channel 20. The aqueous solution passes through this hollow channel 20 as a path and flows in the direction of axis A while in contact with the radially inward-facing surface S5 of the inner layer 3. The intermediate layer 2 is bonded to the inner layer 3 and the outer layer 1, holding them together.

[0032]

[0048] The inner layer 3 provides a surface S5 that is in contact with a radially inward-facing fluid, and the thickness of the inner layer 3 is typically in the range of a cross-sectional thickness T1 of approximately 0.00254 cm (0.001 inches) to approximately 0.0635 cm (0.025 inches). The intermediate layer 2 is typically in the range of a cross-sectional thickness T2 of approximately 0.00254 cm (0.001 inches) to approximately 0.0635 cm (0.025 inches). The outer layer 1 is typically in the range of a cross-sectional thickness T3 of approximately 0.00254 cm (0.001 inches) to approximately 0.0635 cm (0.025 inches).

[0033]

[0049] Polypropylene materials are preferably homopolymers or copolymers of propene and ethene, or mixtures thereof. A typical polypropylene material is Ineos R01C.

[0034]

[0050] Polyurethane elastomers (TPUs) are typically reaction products of polyols and isocyanates and usually contain a combination of hard and soft segment domains. Aromatic polyether-based TPUs or aliphatic polyether-based TPUs, such as polytetramethylene glycol-based polyurethanes, can be used. Preferred TPUs include the Pellethane 2363-80AE series available from Lubrizol Corporation, such as Lubrizol TPU Pellethane 2363-90AE and BASF 1190A.

[0035]

[0051] The thickness of each layer of the pipe material 10 can be controlled by extrusion equipment used, such as a "Tri Die" extruder manufactured by the Genca Division of General Cable Company, Clearwater, Fla. The extruder is selected to provide uniform thickness of layers 1, 2, and 3 along substantially the entire axial length L of all three layers 1, 2, and 3.

[0036]

[0052] The polymer material comprising layers 1, 2, and 3 is selected to have a clear or transparent appearance and to be manually bendable around the axis A of the pipe. The polymer material is also selected to maintain the integrity (i.e., no delamination) and transparency or clarity of the pipe 10 after being subjected to ethylene oxide (EtO) and gamma-ray irradiation sterilization processes.

[0037]

[0053] Figure 3 is a photograph of a cross-section of a tube having a polypropylene inner layer, an EMAC intermediate layer, and an outer layer of either TPU or COC. The photograph of the tube on the left has an outer layer of polyurethane material, an EMAC intermediate layer, and an inner layer of polypropylene material. As can be seen from the cross-section of the tube subjected to high tension pulled by a Lloyd instrument, the three layers remain substantially bonded to each other. Furthermore, as shown in Figure 3, the tube on the right has the same polypropylene inner layer material and the same EMAC intermediate layer material, but has an outer layer made of cyclic olefin copolymer (COC) material. As shown, the three layers of this tube remain substantially bonded to each other, similar to the tube on the left.

[0038]

[0054] Further testing of various embodiments of the present invention is described below and illustrated in Figure 4-10. Various materials and layer structures of two-material, two-layer (2M2L) tubes of the present invention were used for sample and comparative samples of three-material, three-layer (3M3L) tubes described below: material: PP Flint Hills 23R2 • EMAC EMAC SP2268 EVA Celanese 2604A EVA Celanese 2803A TPU Texin RXT90A sample: SR2604 (2M2L) comparison PP Flint Hills 23R2 TPU Texin RXT90A SR2597(3M3L) PP Flint Hills 23R2 EMAC SP2268 TPU Texin RXT90A SR2605(3M3L) PP Flint Hills 23R2 EVA Celanese 2604A TPU Texin RXT90A SR2606(3M3L) PP Flint Hills 23R2 EVA Celanese 2803A TPU Texin RXT90A

[0055] Figure 4 is a matrix or chart showing the layer thickness and composition of one embodiment (SR #2597), a comparative 2M2L embodiment (SR #2604), and two further embodiments (SR #2605 and SR #2606) of a 3M3L tube having an EMAC intermediate layer according to the present invention.

[0039]

[0056] Figure 5 visually shows the layer separation measured under a microscope for each tube that was sandwiched, rotated 10 times, and then aged for 3 days in distilled water at 60 degrees Celsius (L, unit 0.0254 mm = 1 mil (n=5)). It is a side view of two sample tubes, namely the 3M3L SR#2597 according to the present invention on the left and the comparative 2M2L on the right. The sample of the present invention on the left had an L value of 0.11049 mm (4.350 mil), while the comparative tube on the right had a much larger L value of 1.3120624 mm (51.656 mil) (significantly larger layer separation compared to the 2M2L tube).

[0040]

[0057] Figure 6 is a matrix or chart showing side-microscope measurements (L, unit 0.0254 mm = 1 mil), similar to Figure 4, listing five samples for each of SR#2597 (invention, 3M3L, with EMAC interlayer), SR#2604 (2M2L, comparison), and SR#2605 and SR#2606 (invention, 3M3L, with EVA interlayer), with the average L value of the five samples for each group listed, again showing that the 3M3L samples have much lower layer separation L values ​​than the 2M2L samples.

[0041]

[0058] Figure 7 shows 200X microscope cross-sectional views of two sample tubes, namely 3M3L SR#2597 according to the present invention on the left and 2M2L SR#2604 for comparison on the right, visually showing the stratification along with the visual evaluation grade (grade 1-5) for each tube after being sandwiched and rotated 10 times and then aged in distilled water at 60 degrees Celsius for 3 days. The sample of the present invention on the left had a grade of 2.5, while the comparison tube on the right had a much higher grade value of 4.75 (lower values ​​are desirable).

[0042]

[0059] Figure 8, similar to Figure 6, is a matrix or chart showing the visual evaluation grade of the cross-section, listing five samples for each of SR#2597 (invention, 3M3L, with EMAC interlayer), SR#2604 (2M2L, comparison), and Sr#2605 and SR#2606 (invention, 3M3L, with EVA interlayer), and listing the average grade values ​​for each group of the five samples, again showing that the 3M3L samples have a much lower layer separation L value than the 2M2L samples.

[0043]

[0060] Figure 9 is a graph showing the tensile curves for one 2M2L (SR#2604) and various 3M3L tubes (EMAC SR#2597, EVA SR#2605, and EVA SR#2606), each with a different intermediate layer. The tubes were set up for insulin delivery, with stress (psi) on the vertical axis and strain (%) on the horizontal axis. All 3M3L tubes showed much lower layer separation (also known as sleeving) than the 2M2L sample.

[0044]

[0061] Figure 10 is a matrix or chart showing various tensile properties for the different tubes shown in Figure 8, namely 2M2L (SR#2604) and 3M3L tubes with different intermediate layers (EMAC SR#2597, EVA SR#2605, and EVA SR#2606). All 3M3L tubes showed much better tensile properties and lower layer separation (also known as sleeving) than the 2M2L samples.

[0045]

[0062] In various embodiments, the intermediate layer typically acts as a barrier to the movement of mobile components between or from the layer and central channel, where the mobile components include monomers, short-chain polymers, ions, water, small organic molecules, metals, plasticizers, and catalysts.

[0046]

[0063] In various embodiments, layers of polymer material are co-extruded together to form a tubular material such that the outer and inner layers are bonded to an intermediate layer and bonded to each other by bonding to the intermediate layer. The tubular material is formed with a central hollow channel, hole, or passage that is radially surrounded and defined by polymer layers that act as walls for the tubular material.

[0047]

[0064] Referring to Figures 1 and 2, preferably the outer layer 1 has a thickness T3 of approximately 0.00254 cm (0.001") to approximately 0.0635 cm (0.025"), the inner layer 3 has a thickness T1 of approximately 0.00254 cm (0.001") to approximately 0.0635 cm (0.025"), and the intermediate layer 2 has a thickness T2 of approximately 0.00254 cm (0.001") to approximately 0.0635 cm (0.025"). Layers 1, 2, and 3 together form a tubular wall that surrounds and defines the central fluid channel 20.

[0048]

[0065] The polymer material is preferably "contaminant-free," i.e., does not contain more than a non-significant amount of potentially unwanted substances (typically less than about 0.5% by weight, preferably less than about 0.2%), and / or prevents unwanted substances such as plasticizers, catalysts, monomers, metals, salts, ions, or other potentially undesirable substances to humans from leaching or leaking into aqueous solutions or media that one or others of the three layers may come into contact with during normal use of the tubing material for delivering aqueous fluids such as insulin, chemotherapeutic drugs, and other potentially unstable aqueous drug suspensions to or from human subjects. In addition to acting as an adhesive between the outer and inner layers and adhering to these layers, the intermediate layer prevents delamination between the outer and inner layers from the intermediate layer under relatively low to moderate stress or strain conditions. Furthermore, the intermediate layer acts as a barrier against contaminants leaching or leaking from the outer layer to the inner layer, or through the inner layer into the hollow central hole or passage of the tube.

[0049]

[0066] Polypropylene materials typically consist of one or more polypropylene homopolymers and polypropylene copolymers.

[0067] Ethylene vinyl acetate (EVA), ethylene ethyl acrylate copolymer (EEA), ethylene methyl acrylate (EMA) copolymer, and anhydride-grafted ethylene methyl acrylate (AEMA) copolymer possess elastomeric properties and excellent visual clarity. In a typical 3M3L co-extrusion process, TPU, EVA, EEA or EMA or AEMA and PP are melt-extruded through a die head to form tubular extrusions, which are then cooled through a conventional water bath or water vacuum tank, and subsequently wound or cut to specific lengths for use. The level of elasticity and softness of EVA, EEA, EMA, AEMA, or these copolymers is controlled by the amount of vinyl acetate, ethyl acrylate, or methyl acrylate comonomers used with ethylene in the copolymerization process. The three-layer tubes produced by this co-extrusion process return to near their original shape and dimensions after being pulled or stretched along the longitudinal axis of the tube with a stress of approximately 20 MPa or less and a strain of approximately 400% or less using a tensile method, and also act monolithically in that there is no visual delamination between any of the layers after being immersed in water at approximately 60°C for approximately 36 hours.

[0050]

[0068] Cyclic olefin copolymers are typically: Chain copolymerization of cyclic monomers and ethenes, or Ring-opening metathesis polymerization of cyclic monomers and subsequent hydrogenation It is produced by [unspecified method].

[0051]

[0069] Cyclic olefin copolymers are: Chain copolymerization of a cyclic monomer consisting of one or more of 8,9,10-trinorborn-2-ene and 1,2,3,4,4a,5,8,8a-octahydro-1,4:5,8-dimethanonaphthalene with ethene, or Ring-opening metathesis polymerization of cyclic monomers and subsequent hydrogenation It can be produced by [method].

[0052]

[0070] The foregoing description is for illustrative purposes only and is not intended to limit the scope of the present invention. Those skilled in the art will understand that equivalents are anticipated by the foregoing description, and that changes and modifications may be made without departing from the present invention, and that all such equivalents, changes and modifications fall within the scope of the following claims. This specification includes the disclosure of the following inventions. [Item 1] A tube (10) suitable for in vivo transport of aqueous fluid to a target, comprising an inner layer (3), an intermediate layer (2), and an outer layer (1), Formed by a co-extrusion process, the inner layer (3), intermediate layer (2), and outer layer (1) are concentric, and the inner layer (3) and outer layer (1) are bonded to the intermediate layer (2), and are bonded to each other by being bonded to the intermediate layer (2). The inner layer (3) contains polypropylene. The outer layer (1) contains thermoplastic polyurethane, The intermediate layer (2) is selected from one or more of ethylene vinyl acetate copolymer, ethylene acrylate copolymer, ethylene-acrylate maleic anhydride terpolymer, ethylene-acrylate glycidyl methacrylate terpolymer, and maleic anhydride grafted polypropylene, in the tube. [Item 2] The tube according to item 1, wherein the intermediate layer (2) comprises ethylene ethyl acrylate copolymer, ethylene methyl acrylate copolymer, anhydrous grafted ethylene methyl acrylate copolymer, two or more copolymers of the acrylate, or a mixture of two or more thereof. [Item 3] The tube described in item 1, wherein the intermediate layer (2) contains ethylene vinyl acetate. [Item 4] The tube (10) described in item 1, wherein the inner layer (3) contains more than 90% by weight of polypropylene homopolymer or polypropylene copolymer, the outer layer (1) contains more than 90% by weight of aromatic or aliphatic polyether polyurethane, and the intermediate layer (2) contains more than 90% by weight of one or more of ethylene vinyl acetate copolymer, ethylene acrylate copolymer, ethylene-acrylate maleic anhydride terpolymer, ethylene-acrylate glycidyl methacrylate terpolymer, and maleic anhydride grafted polypropylene. [Item 5] The tube according to item 4, wherein the intermediate layer (2) comprises an ethylene ethyl acrylate copolymer having an ethyl acrylate content of at least 19.5 weight percent. [Item 6] The tube described in item 4, wherein the intermediate layer (2) contains more than 90% by weight of ethylene methyl acrylate copolymer. [Item 7] The tube according to item 4, wherein the intermediate layer (2) contains ethylene vinyl acetate having a vinyl acetate content of at least 19.5 weight percent. [Item 8] The tube according to item 1, wherein the inner layer (3) contains more than 90% by weight of a polypropylene homopolymer or polypropylene copolymer or a mixture of the said polypropylene homopolymer and copolymer, and the outer layer (1) contains more than 90% by weight of a polytetramethylene glycol-based polyurethane. [Item 9] The tube described in item 1, having a polyurethane outer layer thickness of 0.0254 to 0.635 mm (0.001 to 0.025 inches), an inner polypropylene layer thickness of 0.0254 to 0.635 mm (0.001 to 0.025 inches), and an intermediate layer thickness of 0.0254 to 0.635 mm (0.001 to 0.025 inches). [Item 10] The tube described in item 1, wherein the inner layer (3) and outer layer (1) do not visually delaminate from the intermediate layer (2) under stresses of 20 MPa or less and strains of 400% or less. [Item 11] A tube as described in item 1 that does not visually delaminate when immersed in water at 60°C for 72 hours. [Item 12] The tube (10) according to item 1, wherein the tube (10) has a central axial fluid channel, the central axial fluid channel is a path for aqueous fluid to pass through, the inner layer (3) has radially inwardly facing walls that come into contact with the aqueous fluid, the outer layer (1) and inner layer (3) resist delamination from the intermediate layer (2) at stresses of 20 MPa or less and strains of 400% or less, and the tube (10) does not visually delaminate after being immersed in water at 60°C for 72 hours. [Item 13] The tube described in item 1, wherein the inner layer (3) and outer layer (1) do not visually delaminate from the intermediate layer (2) under stress of 20 MPa or less and strain of 400% or less, and do not visually delaminate after being immersed in water at 60°C for 72 hours. [Item 14] The tube described in item 1, wherein the outer layer (1) contains more than 90% by weight of aromatic polyether polyurethane and does not visually delaminate after being immersed in water at 60°C for 72 hours. [Item 15] A method for delivering aqueous fluids in vivo: The step of selecting one or more aqueous compositions effective for treating the target condition, wherein the aqueous composition is selected from the group consisting of aqueous drug suspensions, aqueous compositions containing chemotherapeutic agents, and aqueous compositions containing insulin. The steps include delivering one or more selected aqueous compositions to a target through a tube via a flow through the tube described in item 1, Methods that include... [Item 16] A method for forming a medical tube that is transparent or clear in appearance and can be manually bent for in vivo transport of aqueous fluids, The steps include selecting a first polymer material which is an aromatic or aliphatic polyether-based polyurethane material having specific structural stability; The steps include selecting a second polymer material, which is a polypropylene material that is inert to aqueous fluids; The steps include selecting a third polymer material having elastomeric properties and a transparent appearance, which is selected from one or more of ethylene vinyl acetate copolymer, ethylene acrylate copolymer, ethylene-acrylate maleic anhydride terpolymer, ethylene-acrylate methacrylate glycidyl terpolymer, and maleic anhydride grafted polypropylene, The steps include co-extruding selected first, second, and third polymer materials to form bonded outer, inner, and intermediate layers of a medical tube, wherein the outer layer contains at least 90% by weight of the first polymer material, the inner layer contains at least 90% by weight of the second polymer material, and the intermediate layer contains at least 90% by weight of the third polymer material. Includes, The materials are selected to maintain the integrity of the tube against delamination and to maintain a clear or transparent appearance after being subjected to one or more ethylene oxide and gamma irradiation sterilization. A medical tube has a central axial fluid channel defined by radially inward-facing walls of the inner layer, the central axial fluid channel transports aqueous fluid, and the tube does not visually delaminate after being immersed in water at 60°C for 72 hours, and subsequently mechanically flattened by manually crushing it from its normal round cross-sectional state to an oval cross-sectional shape or state. [Item 17] A tube (10) suitable for in vivo transport of aqueous fluid to a target, comprising an inner layer (3), an intermediate layer (2), and an outer layer (1), The tube is formed by a co-extrusion process, and the inner layer (3), intermediate layer (2), and outer layer (1) are concentric, and the inner layer (3) and outer layer (1) are bonded to each other by being bonded to the intermediate layer (2). The inner layer (3) contains polypropylene. The outer layer (1) contains a cyclic olefin copolymer. The intermediate layer (2) is selected from one or more of ethylene vinyl acetate copolymer, ethylene acrylate copolymer, ethylene-acrylate maleic anhydride terpolymer, ethylene-acrylate glycidyl methacrylate terpolymer, and maleic anhydride grafted polypropylene, in the tube (10). [Item 18] A tube (10) as described in item 17, wherein the inner layer (3) contains more than 90% by weight of polypropylene homopolymer or polypropylene copolymer, the outer layer (1) contains more than 90% by weight of cyclic olefin copolymer, and the intermediate layer (2) contains more than 90% by weight of one or more of ethylene vinyl acetate copolymer, ethylene acrylate copolymer, ethylene-acrylate maleic anhydride terpolymer, ethylene-acrylate glycidyl methacrylate terpolymer, and maleic anhydride grafted polypropylene. [Item 19] The tube described in item 17, wherein the inner layer (3) and outer layer (1) do not visually delaminate from the intermediate layer (2) under stress of 20 MPa or less and strain of 400% or less, and do not visually delaminate after being immersed in water at 60°C for 72 hours. [Item 20] A method for delivering aqueous fluids in vivo: The step of selecting one or more aqueous compositions effective for treating the target condition, wherein the aqueous composition is selected from the group consisting of aqueous drug suspensions, aqueous compositions containing chemotherapeutic agents, and aqueous compositions containing insulin. Step 17: Delivering one or more selected aqueous compositions to a target through a tube via a flow through the tube. A method that includes [this]. [Item 21] A method for forming a medical tube that is transparent or clear in appearance and can be manually bent for in vivo transport of aqueous fluids, The steps include selecting a first polymer material which is an aromatic or aliphatic polyether-based polyurethane material having specific structural stability; The steps include selecting a second polymer material, which is a polypropylene material that is inert to aqueous fluids; The steps include selecting a third polymer material having elastomeric properties and a transparent appearance, comprising an acrylate copolymer selected from one or more of ethylene vinyl acetate copolymer, ethylene acrylate copolymer, ethylene-acrylate maleic anhydride terpolymer, ethylene-acrylate methacrylate glycidyl terpolymer, and maleic anhydride grafted polypropylene, The steps include co-extruding selected first, second, and third polymer materials to form bonded outer, inner, and intermediate layers of a medical tube, wherein the outer layer contains at least 90% by weight of the first polymer material, the inner layer contains at least 90% by weight of the second polymer material, and the intermediate layer contains at least 90% by weight of the third polymer material. Includes, The material is selected to maintain the integrity of the tube against delamination and its clear or transparent appearance after being subjected to one or more ethylene oxide and gamma irradiation sterilization. A medical tube has a central axial fluid channel defined by radially inward-facing walls in the inner layer, the central axial fluid channel transports aqueous fluid, and the tube does not visually delaminate after being immersed in water at 60°C for 72 hours, and subsequently mechanically flattened by manually crushing it from its normal round cross-sectional state to an oval cross-sectional shape or state.

Claims

1. A tube (10) suitable for in vivo transport of aqueous fluid to a target, comprising an inner layer (3), an intermediate layer (2), and an outer layer (1), Formed by a co-extrusion process, the inner layer (3), intermediate layer (2), and outer layer (1) are concentric, and the inner layer (3) and outer layer (1) are bonded to the intermediate layer (2), and are bonded to each other by being bonded to the intermediate layer (2). The inner layer (3) contains polypropylene. The outer layer (1) contains thermoplastic polyurethane, The intermediate layer (2) comprises ethylene ethyl acrylate copolymer, ethylene methyl acrylate copolymer, anhydrous grafted ethylene methyl acrylate copolymer, two or more copolymers of the acrylate, or a mixture of two or more thereof. The inner layer (3) and outer layer (1) do not visually delaminate from the intermediate layer (2) at stresses of 20 MPa or less and strains of 400% or less. A tube that does not visually delaminate when immersed in water at 60°C for 72 hours.

2. The tube (10) according to claim 1, wherein the inner layer (3) contains more than 90% by weight of polypropylene homopolymer or polypropylene copolymer, the outer layer (1) contains more than 90% by weight of aromatic or aliphatic polyether polyurethane, and the intermediate layer (2) contains more than 90% by weight of one or more of ethylene ethyl acrylate copolymer, ethylene methyl acrylate copolymer, anhydride-grafted ethylene methyl acrylate copolymer, two or more copolymers of the acrylate, or a mixture of two or more thereof.

3. The tube according to claim 2, wherein the intermediate layer (2) comprises an ethylene ethyl acrylate copolymer having an ethyl acrylate content of at least 19.5% by weight.

4. The tube according to claim 2, wherein the intermediate layer (2) contains more than 90% by weight of ethylene methyl acrylate copolymer.

5. The tube according to claim 1, wherein the inner layer (3) contains more than 90% by weight of a polypropylene homopolymer, a polypropylene copolymer, or a mixture of the polypropylene homopolymer and copolymer, and the outer layer (1) contains more than 90% by weight of a polytetramethylene glycol-based polyurethane.

6. The tube according to claim 1, wherein the thickness of the polyurethane outer layer is 0.0254 to 0.635 mm (0.001 to 0.025 inches), the thickness of the inner polypropylene layer is 0.0254 to 0.635 mm (0.001 to 0.025 inches), and the thickness of the intermediate layer is 0.0254 to 0.635 mm (0.001 to 0.025 inches).

7. The tube according to claim 1, wherein the tube (10) has a central axial fluid channel, the central axial fluid channel is a path for an aqueous fluid to pass through, the inner layer (3) has radially inwardly facing walls that come into contact with the aqueous fluid, the outer layer (1) and inner layer (3) resist delamination from the intermediate layer (2) at stresses of 20 MPa or less and strains of 400% or less, and the tube (10) does not visually delaminate after being immersed in water at 60°C for 72 hours.

8. The tube according to claim 1, wherein the outer layer (1) contains more than 90% by weight of aromatic polyether polyurethane and does not visually delaminate after being immersed in water at 60°C for 72 hours.

9. A method for forming a medical tube that is transparent or clear in appearance and can be manually bent for in vivo transport of aqueous fluids, The steps include selecting a first polymer material which is an aromatic or aliphatic polyether-based polyurethane material having specific structural stability; The steps include selecting a second polymer material, which is a polypropylene material that is inert to aqueous fluids; The steps include selecting a third polymer material having elastomeric properties and a transparent appearance, selected from one or more of ethylene ethyl acrylate copolymer, ethylene methyl acrylate copolymer, anhydrous grafted ethylene methyl acrylate copolymer, two or more copolymers of the acrylate, or a mixture of two or more thereof, The steps include co-extruding selected first, second, and third polymer materials to form bonded outer, inner, and intermediate layers of a medical tube, wherein the outer layer contains at least 90% by weight of the first polymer material, the inner layer contains at least 90% by weight of the second polymer material, and the intermediate layer contains at least 90% by weight of the third polymer material. Includes, The materials are selected to maintain the integrity of the tube against delamination and to maintain a clear or transparent appearance after being subjected to one or more ethylene oxide and gamma irradiation sterilization. The medical tube has a central axial fluid channel defined by radially inward-facing walls of the inner layer, the central axial fluid channel transports aqueous fluid, and the tube is immersed in water at 60°C for 72 hours, and then mechanically flattened by being crushed from its normal round cross-sectional state to an oval cross-sectional shape or state by manual crushing, and does not visually delaminate. A method for preventing visual delamination from the intermediate layer in the inner and outer layers under stresses of 20 MPa or less and strains of 400% or less.

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