Core wire for a guide wire comprising a functionally graded alloy

Abstract

Guide wires and catheters made from a functionally graded alloy comprising 3-10 weight % Al and 5-20 weight % Mn, the balance being substantially Cu and inevitable impurities. The functionally graded alloy is produced by forming the copper-based alloy, maintaining it at a temperature of at least 500° C. and rapidly cooling it, and then subjecting the alloy to an aging treatment by a gradient temperature heater.

Description

FIELD OF THE INVENTION

[0002] The present invention relates to a core wire for a guide wire based on a copper-based, functionally graded ally having uniform composition and diameter and continuously or stepwise changing properties such as hardness, modulus elongation, etc. These guide wires can be used in catheters and the like.

BACKGROUND OF THE INVENTION

[0003] Functionally graded alloys are materials having continuously or stepwise changing properties such as hardness, elasticity, thermal conductivity, electrical conductivity, etc., without developing a gradient in size with mechanical working such as cutting or the like, or chemical treatment such as etching or the like. Functionally graded materials developed to date are mostly two-component composites such as SiC/C, ZrO/W, TiC/Ni, ZrO/Ni, etc. These materials have gradually changing mixing ratios.

[0004] Conventional functionally graded materials having gradually changing mixing ratios have been produced by mixing different material powders at gradually changing mixing ratios to prepare a plurality of mixed powder sheets having gradually changing mixing ratios, laminating the mixed powder sheets along the gradually changing mixing ratios, compacting them, and sintering them. For example, Japanese Laid-Open Patent No. 5-278158 discloses a functionally graded, binary metal material produced by laminating and sintering tungsten powder and molybdenum powder at a gradually changing mixing ratio.

[0005] However, functionally graded materials produced by this method cannot be rolled or drawn, and they can be formed into desired shapes only by cutting. Thus, they are not only very expensive, but they also cannot be formed into complicated shapes. Accordingly, conventional functionally graded materials are used mainly in highly expensive applications, such as spacecraft, nuclear power generators, etc. Thus, it is very desirable to develop less expensive and easily formable functionally graded materials.

[0006] Alloys having shape recovery properties and superelasticity are widely used in various applications such as guide wires, catheters, etc. To introduce a catheter into a blood vessel and place it at a desired site in the blood vessel, a guide wire for guiding the catheter is first introduced into the desired site in the blood vessel, and the catheter is guided to the desired site in the blood vessel along the guide wire. Because human blood vessels wind and branch differently depending upon the individual, guide wires having high introduction operability and torque conveyance are required to insert the guide wires without damaging the blood vessel walls.

[0007] For this purpose, a guide wire is composed of a core wire comprising a tip end potion which is made soft by reducing its diameter, and a body portion which is relatively rigid. A coating layer is formed on the core wire, the coating being made of a synthetic resin which is inert with respect to the human body, such as polyamides, thermoplastic polyurethanes, fluoroplastics, etc.

[0008] The guide wire usually comprises a coil-shaped metal wire made of a material such as carbon steel or stainless steel. However, since wires made of these materials are easily bent, superelastic metals such as Ni—Ti alloys and the like are used for the core wires of guide wires (Japanese Patent Publication No. 2-24549). However, superelastic Ni—Ti alloys lack rigidity, even though they are sufficiently soft for this use. Therefore, they are not useful for insertion into a blood vessel, sometimes making it difficult to place them at a desired location in the blood vessel.

[0009] Additionally, because Ni—Ti alloys are relatively poor with respect to cold working, they are not easily formed into thin wires suitable for use as guide wires and the like. With respect to the gradient properties from heat treatment, it is difficult to provide the guide wire with the gradient needed to control the torque conveyance of the guide wire.

[0010] The same is true of catheters made of Ni—Ti alloys. The Ni—Ti alloy catheters are not easily inserted into a blood vessel. Also, Ni—Ti alloys cannot be easily formed into thin wires or pipes. Furthermore, the Ni—Ti alloys are poor in weldability and adhesion, posing problems when combined with other materials.

SUMMARY OF THE INVENTION

[0011] It is an object of the present invention to provide an inexpensive functionally graded alloy having excellent workability and a method for producing such a functionally graded alloy.

[0012] It is another object of the present invention to provide a core wire for a guide wire comprising a soft tip end portion and a properly elastic and rigid body portion which is readily insertable and has excellent torque conveyance and workability, as well as a guide wire comprising such a core wire.

[0013] It is a further object of the present invention to provide a catheter comprising a soft tip end portion and a properly elastic and rigid body portion which is readily insertable, and has excellent torque conveyance and workability.

[0014] As a result of research on previously proposed shape memory alloy Cr—Al—Mn having a β-phase structure (Japanese Laid-Open Patent No. 7-62472), the inventors have found that when the shape memory Cu—Al—Mn alloy having a β-phase structure is partially heated at particular temperatures or at gradually changing temperatures, the shape memory Cu—Mn—Al is provided with a partially different crystal structure, which exhibits remarkably gradient properties. The present inventors have also found that by giving gradually changing properties to the Cu—Al—Mn alloy by heat treating the alloy at a proper temperature gradient, guide wires and catheters can be produced from this Cu—Al—Mn alloy which have improved insertion capabilities and torque conveyance. The present invention has been completed based upon these findings.

[0015] The functionally graded alloy of the present invention has a composition comprising 3-10 weight % Al, 5-20 weight % of Mn, with the balance Cu and inevitable impurities. The alloy comprises a first portion composed essentially of a β-phase, a second portion composed essentially of an α-phase and a Heusler phase, and a third portion having a crystal structure continuously or stepwise changing from the first portion to the second portion.

[0016] The method for producing the functionally graded alloy according to the present invention comprises the steps of:

[0017] a. forming a copper-based alloy having a composition comprising 3-10 weight % Al, 5-20 weight % of Mn, the balance being substantially Cu and inevitable impurities, into a desired shape;

[0018] b. maintaining the copper-based alloy at a temperature of 500° C. or more and rapidly cooling the alloy to transform the crystal structure thereof substantially to a β-phase; and

[0019] c. subjecting the copper-based alloy to an aging treatment in a heater having a temperature gradient, thereby heating the first portion to less than 250° C., the second portion to 250-350° C., and the third portion to a temperature continuously or stepwise changing from the heating temperature of the first portion to the heating temperature of the second portion.

[0020] A core wire for a guide wire according to the present invention comprises a body portion having high rigidity and a tip end portion having a lower rigidity than that of the body portion, at least part of the core wire being made of a copper-based alloy comprising 3-10 weight % of Al, 5-20 weight % of Mn, with the balance being substantially Cu and inevitable impurities.

[0021] The guide wire according to the present invention comprises a core wire comprising a body portion having high rigidity and a tip end portion having a lower rigidity than that of the body portion, at least part of the core wire being made of a copper-based alloy comprising 3-10 weight % of Al, 5-20 weight % of Mn, with the balance being substantially Cu and inevitable impurities.

[0022] A catheter according to one embodiment of the present invention is at least partially constituted by a metal pipe, the metal pipe having at least a tip end portion made of a copper-based alloy comprsiing 3-10 weight % of Al, 5-20 weight % of Mn, with the balance being substantially Cu and inevitable impurities.

[0023] A catheter according to another embodiment of the present invention contains a reinforcing metal member in at least part of the catheter tube, the reinforcing metal member being made of a copper-based alloy comprising 3-10 weight % of Al, 5-20 weight % of Mn, with the balance being substantially Cu and inevitable impurities.

BRIEF DESCRIPTION OF THE DRAWINGS

[0024] FIG. 1 is a schematic view showing an example of a gradient temperature heater.

[0025] FIG. 2 is a graph showing the hardness distribution and the aging temperature distribution of the functionally graded alloy wire of Sample No. 3 in Example 1.

[0026] FIG. 3 is an optical photomicrograph showing the microstructure of the low-aging temperature portion of the functionally graded alloy of Sample No. 1 in Example 1.

[0027] FIG. 4 is an optical photomicrograph showing the microstructure of the high-aging temperature portion of the functionally graded alloy of Sample No. 1 in Example 1.

[0028] FIG. 5 is a graph showing the relation between the aging temperature and the hardness of Samples Nos. 2 and 3 in Example 2.

[0029] FIG. 6 is a graph showing the relation between the aging time and the hardness of Samples Nos. 5 and 6 in Example 3.

[0030] FIG. 7 is a schematic view showing one example of the core wire for a guide wire according to the present invention.

[0031] FIG. 8 is a schematic view showing another example of the core wire for a guide wire according to the present invention.

[0032] FIG. 9 is a schematic view showing one example of the guide wire according to the present invention.

[0033] FIG. 10 is an enlarged cross-sectional view showing another example of the guide wire according to the present invention.

[0034] FIG. 11 is a schematic view showing a further example of the guide wire according to the present invention.

[0035] FIG. 12 is an enlarged cross-sectional view showing a further example of the guide wire according to the present invention.

[0036] FIG. 13 is an A-B cross-sectional view of FIG. 12.

[0037] FIG. 14 is a schematic view showing an example of a catheter according to the present invention.

[0038] FIG. 15 is an enlarged A-A′ cross-sectional view of FIG. 14.

[0039] FIG. 16 is a schematic view showing another example of a catheter according to the present invention.

[0040] FIG. 17 is an enlarged B-B′ cross-sectional view of FIG. 16.

[0041] FIG. 18 is an enlarged C-C′ cross-sectional view of FIG. 16.

[0042] FIG. 19 is a schematic view showing a further example of a catheter according to the present invention.

[0043] FIG. 20 is a schematic view showing a further example of a PTCA catheter equipped with a balloon according to the present invention.

[0044] FIG. 21 is an enlarged D-D′ cross-sectional view of FIG. 20.

[0045] FIG. 22 is an enlarged E-E′ cross-sectional view of FIG. 20.

[0046] FIG. 23 is a schematic view showing another example of a catheter according to the present invention.

[0047] FIG. 24 is an enlarged F-F′ cross-sectional view of FIG. 23.

[0048] FIG. 25 is a schematic view showing a further example of a catheter according to the present invention.

[0049] FIG. 26 is an enlarged G-G′ cross-sectional view of FIG. 25.

[0050] FIG. 26 is an enlarged G-G′ cross-sectional view of FIG. 25.

[0051] FIG. 27 is a schematic view showing a further example of a catheter according to the present invention.

[0052] FIG. 28 is a partial enlarged cross-sectional view of FIG. 27.

[0053] FIG. 29 is a schematic view showing a further example of a catheter according to the present invention.

[0054] FIG. 30 is an enlarged H-H′ cross-sectional view of FIG. 29.

[0055] FIG. 31 is a schematic view showing a further example of a catheter according to the present invention.

[0056] FIG. 32 is an enlarged I-I′ cross-sectional view of FIG. 31.

DETAILED DESCRIPTION OF THE INVENTION

[0057] [1] Composition of the Functionally Graded Alloy

[0058] The functionally graded alloy of the present invention contains 3-10 weight % of Al, 5-20 weight % of Mn, with the balance being substantially Cu and inevitable impurities. Although the functionally graded alloy has a β-phase structure [body-centered cubic (bcc) structure], at high temperatures a martensitic transformation without diffusion occurs at low temperatures. Specifically, the β-phase structure is changed to a dual-phase structure of an α-phase [face-centered cubic (fcc) structure] and a Heusler phase [ordered body-centered cubic (fcc) structure] by heating at about 300° C.

[0059] When the aluminum content is less than 3 weight %, the beta-phase cannot be formed. On the other hand, when the aluminum content exceeds 10 weight %, the resultant alloy becomes extremely brittle. The preferred aluminum content is 6-10 weight %, although it may be changed depending on the amount of manganese.

[0060] The inclusion of manganese makes the range of the β-phase shift toward a low aluminum region, thereby remarkably improving the cold workability of the alloy, which makes it easy to form the alloy. When the manganese content is less than 5 weight %, sufficient workability cannot be obtained, failing to form the region of the β-phase. On the other hand, when the manganese exceeds 20 weight %, sufficient shape recovery properties cannot be obtained. The preferred manganese content is 8-12 weight %.

[0061] The Cu—Al—Mn alloy having the above composition have a good hot- and cold-workability, achieving a cold working ratio of 20 to 90% or more. This enables the formation of extremely thin wires, sheets, pipes, etc., which has conventionally been difficult.

[0062] In addition to the above components, the functionally graded alloy of the present invention may further contain at least one element selected from the group consisting of Ni, Co, Fe, Ti, V, Cr, Si, Nb, W, Sn, Ag, Mg, P, Zr, Zn, B, and misch metals. These elements act to make crystal grains fine while maintaining the cold workability of the functionally graded alloy, thereby improving the strength of the alloy. The total content of these additional elements is preferably 0.001-10 weight %, particularly 0.001-5 weight %. When the total content of these elements exceeds 10 weight %, the martensitic transformation temperature of the alloy lowers, making the β-phase structure unstable.

[0063] Ni, Co, Fe and Sn are elements which are effective for strengthening the matrix structure of the alloy. The preferred content is 0.001-3 weight % for each of Ni and Fe. Although Co acts to make the crystal grains fine by the formation of Co—Al, an excess amount of co reduces the toughness of the alloy. Thus, the preferred content of Co is 0.001-2 weight %. Additionally, the preferred content of Sn is 0.001-1 weight %.

[0064] Ti is combined with harmful elements such as N and O to form oxynitrides. When Ti is added together with B, they form borides which function to make the crystal grains fine, thereby improving the shape recovery ratio of the alloy. The preferred Ti content is 0.001-2 weight %.

[0065] V, Nb, Mo and Zr increase the hardness of the alloy, thereby improving the wear resistance of the alloy. Because these elements are not substantially dissolved in the matrix, they are deposited as bcc crystals, effective in making th3e crystal grains fine. The preferred content of each of V, Nb, Mo and Zr is 0.001-1 weight %.

[0066] Cr is effective in maintaining the wear resistance and the corrosion resistance of the alloy. The preferred Cr content is 0.001-2 weight %.

[0067] Si increases the corrosion resistance of the alloy. The preferred Si content is 0.001-2 weight %.

[0068] W improves the deposition strengthening of the alloy because W is not substantially dissolved in the matrix. The preferred W content is 0.001-1 weight %.

[0069] Mg removes harmful elements such as N and O and fixes harmful elements sulfur as sulfides, thereby improving the hot workability and the toughness of the alloy. However, and excess of Mg causes grain boundary segregation, thereby making the alloy brittle. The preferred Mg content is 0.001-0.5 weight %.

[0070] P acts as a deoxidizer, improving the toughness of the alloy. The preferred P content is 0.01-0.5 weight %.

[0071] Zn lowers the shape memory treatment temperatures. The preferred Zn content is 0.001-5 weight %.

[0072] B, which makes the crystal grains fine, is preferably used together with Ti and Zr. The preferred B content is 0.01-0.5 weight %.

[0073] Misch metals make the crystal grains fine. The preferred contents of misch metals is 0.001-2 weight %.

[0074] [2] Production of Functionally Graded Alloy

[0075] a. Forming Copper-based Alloy

[0076] A melt of copper-based alloy having the composition 3-10 weight % of Al, 5-20 weight % of Mn, with the balance being substantially Cu and inevitable impurities is cast and formed into a desirable shape by hot rolling, cold rolling, pressing, etc. The alloy of the present invention has good hot and cold workability, achieving a cold working ratio of 20 to 90% or more. This enables the formation of extremely thin wires, sheets, ribbons, pipes, etc., which conventionally is difficult.

[0077] In the case of a copper-based alloy containing 8-10 weight % of aluminum, an α+β dual-phase structure having excellent workability is formed when the average cooling speed after hot working is 200° C. per minute or less. The copper-based alloy is desirably cooled to the above speed, particularly in a range of 800-400° C. If the cooling speed is faster than this speed, the β-phase is mainly formed in the alloy, which fails to obtain as high a workability as when the α+β dual phase is formed. On the other hand, in the case of a copper-based alloy containing 3-8 weight % of aluminum, the copper-based alloy may be composed only of a β-phase structure after hot working, and the cooling speed after hot working is not limited.

[0078] b. Solution Treatment

[0079] The copper-based alloy is then subjected to heat treatment (solution treatment) at 500° C. or more, preferably 600-900° C., to transform its crystal structure to the β-phase. After heat treatment, the β-phase is frozen by rapid cooling at a rate of 50° C. per second or more. The rapid cooling of the alloy is carried out by immersing the alloy in a cooling medium such as water, or by forced-air cooling. When the cooling speed is less than 50° C. per second, the a-phase deposits in the alloy, failing to maintain the alloy in a state having only β-phase crystal structure, and thus reducing the property gradient. The preferred cooling speed is 200° C. per second or more.

[0080] c. Aging Treatment

[0081] According to the present invention, the aging treatment of the first portion wherein the β-phase crystal structure is maintained is carried out at a temperature of less than 250° C. The aging treatment of the second portion in which the crystal structure is transformed into the dual-phase structure of the α-phase and the Heusler phase is carried out at 250-350° C. The aging treatment of the third portion between the first and second portions is carried out at a continuous or stepwise temperature gradient (temperature distribution) from the heating temperature of the first portion to that of the second portion.

[0082] To meet the above conditions, the aging treatment is preferably carried out in a gradient temperatures heater. FIG. 1 is a schematic view showing an example of such a gradient temperature heater. The gradient temperature heater 1 for the aging treatment of a functionally graded alloy rod 7 comprises a furnace pipe 2, a nichrome wire 3 wound around the furnace pipe 2, a heat-insulating member 4, a plurality of temperature sensors 51, 52, 53, and a power supply/temperature controller 6 connected to the nichrome wire 3 and the temperature sensors 51, 52, 53. In this example, the density gradient of the wound nichrome wire 3 controls the temperature gradient in the furnace pipe 2. To turn one end portion 71 of the alloy rod 7 to a first portion composed essentially of a β-phase, the nichrome wire 3 is wound sparsely around one end portion 21 of the furnace pipe 2. Also, to turn the other end portion 72 of the alloy rod 7 to a second portion composed essentially of an α-phase and a Heusler phase, the wire 3 is wound densely around the other end portion 22 of the furnace pipe 2. Thus, the furnace pipe 2 has a temperature gradient which may be controlled by the power supply/temperature controller 6.

[0083] The heating temperature of the first portion is less than 250° C., preferably 100-200° C. If the heating temperature of the first portion were too low, the β-phase would be unstable, making it likely that the martensitic transformation temperature will change when the alloy is left at room temperature. On the other hand, when the heating temperature is 250° C. or more, the α-phase may be deposited, and thus the difference in properties between the firsts and second portions will not be increased.

[0084] The heating temperature of the second portion is 250-350° C., preferably 280-320° C. When it is less than 250° C., the crystal structure of the second portion is not sufficiently transformed into a dual-phase structure of an α-phase and a Heusler phase, with a failure to increase the difference in properties between the first and second portions. On the other hand, when it is more than 350° C., the crystal structure becomes coarse, and properties such as yield stress, hardness and the like become coarse.

[0085] The difference in heating temperature between the first and second portion is preferably 50° C. or more, particularly 80° C. or more. When it is less than 50° C., the difference in properties between the first and second portions becomes smaller.

[0086] The aging treatment time in general is preferably 1-300 minutes, particularly 5-200 minutes, although this time may vary depending upon the composition of the functionally graded alloy. Less than one minute of aging would not provide sufficient aging effects. On the other hand, when the aging time is more than 300 minutes, the alloy structure becomes too coarse to keep sufficient mechanical properties in the functionally graded material.

[0087] In the case of a core wire for a guide wire, the copper-based alloy core wire may be subjected to an aging treatment in the following two ways: The first aging treatment is to heat the core wire uniformly at 250° C. or less, preferably 100-200° C., such that the core wire has uniform shape recovery properties and superelasticity.

[0088] The second aging treatment is to heat the core wire at different temperatures, such that the core wire has gradient properties. Namely, the core wire has a high-rigidity body portion, a low-rigidity tip end portion, and an intermediate portion between them having rigidity decreasing from the high-rigidity body portion to the low-rigidity tip end portion. The high-rigidity body portion is obtained with an aging treatment at 250-350° C., preferably 280-320° C., and the low-rigidity tip end portion is obtained by an aging treatment at less than 250° C., preferably 100-200° C. The intermediate portion between the body portion and the tip end portion is obtained by an aging treatment at a temperature continuously or stepwise changing from the high-rigidity body portion to the low-rigidity tip end portion. The difference in aging temperature between the high-rigidity body portion and the low-rigidity top end portion is preferably 50° C. or more, particularly 80° C. or more.

[0089] [3] Properties of Functionally Graded Alloy

[0090] (a) Crystal Structure

[0091] The functionally graded alloy of the present invention comprises a first portion composed essentially of a β-phase, a second portion composed essentially of an α-phase and a Heusler phase, and a third portion having a crystal structure continuously or stepwise changing from the first portion to the second portion.

[0092] The term “composed essentially of a β-phase” as used herein means not only a crystal structure consisting only of a β-phase, but also a crystal structure containing, in addition to the β-phase, other phases such as an β-phase, a Heusler phase, borides such as TiB and ZrB, bcc phases of V, Mo, Nb and W, and intermetallic compounds such as NiAl, CoAl, etc. in such small percentages so as not to affect the superelasticity and shape recovery properties of the first portion. The total amount of the α-phase and the Heusler phase is preferably 5 volume % or less. When it exceeds 5 volume %, the superelasticity and shape recovery properties of the first portion are remarkably decreased, thereby making the gradient of the properties smaller.

[0093] Also, the term “composed essentially of a dual phase comprising an α-phase and a Heusler phase” as used herein means not only a crystal structure consisting of only the α-phase and the Heusler phase, but also a crystal structure containing, in addition to the α-phase and the Heusler phase, other phases such as β-phase, borides such as TiB and ZrB, bcc phases of V, Mo, Nb, and W, and intermetallic compounds such as NiAl, CoAl, etc. in such small percentages as not to affect the hardness of the second portion. The amount of the β phase is preferably 10 volume % or less in the second portion.

[0094] The term “continuously or stepwise changing crystal structure” as used herein means that a volume ration of the β-phase to [the α-phase and the Heusler phase] changes continuously or stepwise in the crystal structure. The α-phase and the Heusler phase may be gradually deposited from the β-phase by aging treatment. The higher the aging temperature, and the longer the aging time, the more the α-phase an the Heusler phase are deposited. Whether the crystal structure changes continuously or stepwise in the third portion depends upon the aging temperature distribution and the aging time. When the aging treatment is carried out at a stepwise temperature distribution for a short period of time, the resultant crystal structure changes stepwise. The boundaries between the first and third portions and between the second and third portions are not explicit in the case of the third portion having a continuously changing crystal structure. Because the properties change generally sharply in the third portion, however, the boundaries of the above three portions can relatively easily be determined from the distribution of properties.

[0095] The first portion composed essentially of the β-phase has shape memory properties and superelasticity as described in Japanese Laid-Open Patent No. 7-62472. In contrast thereto, the second portion is composed of a hard material which is resistant to bending and which has completely different properties from the first portion. Although the distance between the first portion and the second portion (i.e., length of the third portion) may arbitrarily be set, it is preferably about 2 cm of more, particularly about 5 cm or more. It is difficult to provide the ageing temperature gradient in a distance of less than 2 cm.

[0096] (b) Differences in Properties

[0097] With respect to some properties, differences between the first portion and the second portion will be described in detail below.

[0098] (i) Hardness

[0099] The first portion preferably has a hardness of less than 350 Hv, and the difference in hardness between the first portion and the second portion can be made as large as 20 Hv or more. However, the hardness of the alloy may vary within the above range, depending upon its composition.

[0100] (ii) Yield Stress

[0101] Because the first portion which is composed essentially of a β-phase which has superelasticity, the yield stress (0.2% offset yield strength) of the first portion is less than 400 Mpa, although it may vary within the range depending upon the composition of the alloy. The difference in yield stress between the first portion and the second portion can be made as large as 50 Mpa or more.

[0102] (iii) Shape Recovery Ratio

[0103] The first portion has excellent shape recovery properties, exhibiting a shape recovery ratio of 80% or more. The shape recovery ration of the second portion is as low as less than 15%, which means there are substantially no shape recovery properties. The difference in shape recovery ratio between the first and second portions can be made as large as 70% or more.

[0104] [iv] Core Wire for Guide Wire

[0105] The core wire for a guide wire comprises a functionally graded copper-based alloy wire having at least a low-rigidity tip end portion and a high-rigidity body portion.

[0106] First embodiment

[0107] In the first embodiment, as shown in FIG. 7, the core wire is a straight copper-based alloy wire having a tip end portion that is not tapered. The core wire 2 is composed of four regions, 2a, 2b, 2c, and 2d, from the base end 3 to the tip end 4. Each region 2a, 2b, 2c, and 2d has rigidity which decreases stepwise from the side of the base end 3 to the side of the tip end 4. Each region may have an arbitrarily set length.

[0108] A gradient-rigidity core wire as shown in FIG. 7 many be formed as described above by hot working and/or cold working, maintaining the temperature of the wire above 500° C. and rapidly quenching the wire, and further aging the wire at different temperatures in the respective regions 2a, 2b, 2c, and 2d. The aging temperature in region 2a is preferably 250-350° C. and the aging temperature in the region 2d is less than 250C. The aging temperatures in regions 2b and 2c are between those for regions 2a and 2d, with the aging temperature in region 2b being higher than that for region 2c.

[0109] Second embodiment

[0110] In the second embodiment, as shown in FIG. 8, the core wire is a copper-based alloy wire composed of four regions 2a, 2b, 2c, and 2d from the base end 3 to the tip end 4. Rigidity decreases in each region 2a, 2b, 2c, and 2d from the side of the base end 3 to the side of the tip end 4. Each region may have an arbitrarily set length.

[0111] As in the first embodiment, region 2a is a high-rigidity region, while region 2d is a low-rigidity region. Regions 2b and 2c have intermediate rigidity between that of regions 2a and 2d, with the rigidity of region 2b being higher than that of region 2c. Because region 2d has a smaller diameter in the second embodiment than in the first embodiment, the softness of the copper-based alloy in region 2d may be less in the second embodiment than in the first embodiment. The core wire of the second embodiment may be produced in the same manner as in the first embodiment.

[0112] Third embodiment

[0113] In the third embodiment, shown in FIG. 9, the core wire comprises a base wire 5 and a core wire 6 connected to each other. The core wire 6 is a copper-based alloy wire, and the base wire 5 may be a flat ribbon made of conventional material such as stainless steel. Ends of the base wire 5 and the core wire 6 are partially overlapped and bonded with a coil, etc.

[0114] The core wire 6 consists of two regions, 6a and 6b, from the base end 7a to the tip end 7b. Region 6a is a high-rigidity region, while region 6b is a region having rigidity continuously decreasing toward the tip end 7b. The core wire 6 is soft (less rigid) and superelastic in the vicinity of tip end 7b. Each region may have an arbitrarily set length.

[0115] As in the first embodiment, core wire 6 is provided with a rigidity gradient by applying different aging temperature to different regions The aging temperature of region 6a is preferably 250-350° C. The aging temperature of region 6b has a temperature distribution which is continuously lowered from base end 7a to tip end 7b. The highest temperature of the above temperature distribution is preferably the same as in region 6a, and the lowest temperature in region 6b is preferably lower than 250° C.

[0116] [5] Catheter

[0117] (a) Catheter Having Copper-based Alloy Pipe

[0118] One catheter according to the present invention is at least partially made of a copper-based alloy pipe. The catheter is relatively rigid in a body portion, and has low rigidity in a tip end portion. The bending modulus of the copper-based alloy pipe decreases continuously or stepwise in a direction from the base end to the tip end of the catheter, and at least a tip end portion of the copper-based alloy pipe has superelasticity.

[0119] The following are specific embodiments of catheters of the present invention.

[0120] (i) First embodiment

[0121] FIG. 14 shows a first example of the catheter of the present invention, and FIG. 15 is an A-A′ cross-sectional view of FIG. 14.

[0122] The body of the catheter is made of a copper-based alloy pipe 42, which has a bending modulus which decreases continuously or stepwise from the base end 43 to the tip end portion 44. The copper-based alloy pipe can be formed from a thicker pipe by gradually reducing the pipe diameter by rolling or drawing.

[0123] Pipe 42 has a high-rigidity body portion 42a, a low-rigidity, superelastic tip end portion 42c, and an intermediate portion 42b between them which has intermediate rigidity. In each region, the rigidity may be uniform or gradually changing.

[0124] A gradient rigidity copper-based alloy pipe can be formed by hot working and/or cold working, keeping the pipe at a temperature of at least 500° C. and rapidly quenching the pipe, and then aging the pipe at different temperatures in different regions. The aging treatment temperature is preferably 250-350° C. in body portion 42a, and less than 250° C. in tip end portion 42c. The aging treatment temperature in intermediate portion 42b is between that of body portion 42a and tip end portion 42c. When a gradient is necessary in each region, the aging treatment temperature should gradually decrease in a direction from base end 43 to tip end 44 of the catheter in each region.

[0125] (ii) Second embodiment

[0126] FIG. 16 shows a second embodiment of a catheter according to the present invention. FIG. 17 is a B-B′ cross-sectional view of FIG. 16, and FIG. 18 is a C-C′ cross-sectional view of FIG. 16.

[0127] Catheter body 51 comprises a copper-based alloy pipe 52, which has a bending modulus which decreases continuously or stepwise from base end 53 to tip end portion 54. Copper-based alloy pipe 52 can be formed from a thicker pipe by gradually reducing the pipe diameter by rolling or drawing. Catheter 51 may be the same as catheter 41 except that tip end portion 52c is tapered.

[0128] (iii) Third embodiment

[0129] FIG. 19 shows a third embodiment of a catheter of the present invention. Catheter 61 is bent at an angle of 90-150° in a tip end position 62 so that the catheter 61 can easily enter into a winding or branched blood vessel. After bending, the copper-based alloy pipe is subjected to a solution treatment and an aging treatment.

[0130] (b) Catheter Having Copper-based Alloy Reinforcing Member

[0131] FIG. 23 shows a second type of catheter according to the present invention. FIG. 24 is an F-F′ cross-sectional view of FIG. 23. The catheter 101 comprises a flexible tube body 111, a hub 112 mounted on a base end of the flexible tube body 111, and a soft tip 113 mounted to a tip end of the flexible tube body 111. The flexible tube body 111 is preferably reinforced by wire- or ribbon-shaped reinforcing copper-based alloy members 115.

[0132] In the embodiment shown in FIG. 24, the tube body 111 comprises an inner layer 114, an intermediate Cu—Al—Mn alloy braid layer 115, and an outer layer 116. While the intermediate Cu—Al—Mn alloy braid 115 is made of eight thin Cu—Al—Mn alloy wires in FIG. 24, there can be any number of thin wires forming the braid. Also, a plurality of straight copper-based alloy wires may be disposed along the length of the catheter 101. The copper-based alloy wires may be in the form of a coil.

[0133] The copper-based alloy reinforcing member has a bending modulus which either decreases continuously or stepwise from the base end to the tip end. Thus, the body portion is a high-rigidity region, the tip end portion is a low-rigidity, superelastic region, and the intermediate portion is a region which has a rigidity intermediate that of the body portion and the tip end portion. In each region, rigidity may be uniform or gradually changing.

[0134] The gradient-rigidity, reinforcing copper-based alloy member can be obtained by aging different regions at different temperatures in the same manner as described above.

[0135] A catheter containing a reinforcing metal member can be produced by co-extruding a resin for the tube body 111 and a reinforcing metal member, or by immersing an inner layer 114 coated with the reinforcing metal member 115 in a resin solution and solidifying the resin to form an outer layer 116.

[0136] [6] Surface Treatment

[0137] The copper-based alloy member such as core wires, guide wires and catheters are preferably coated with Au, Pt, Ti, Pd or TiN by plating or vapor deposition. The copper-based alloy members are preferably coated with polyethylene, polyvinyl chloride, polyesters, polypropylene, polyamides, polyurethane, polystyrene, fluoroplastics, silicon rubbers or their elastomers, or composites thereof. These coating materials preferably contain X-ray contrast media such as barium sulfate. Furthermore, surfaces of the cores wires, guide wires, and catheters are preferably coated with lubricating materials such as polyvinyl pyrrolidone, ethyl maleate, methyl vinyl ether-maleic anhydride copolymer, etc.

[0138] The present invention will be described in detail below referring to the following EXAMPLES, without restricting the scope of the present invention as defined by the claims. These examples are for illustration only, and are not intended to limit the scope of the invention.

EXAMPLE 1

COMPARATIVE EXAMPLE 1

[0139] Copper-based alloys having compositions shown in Table 1 as Sample Nos. 1-7 (Example 1) and Sample No. 8 (Comparative Example 1) were melted, and solidified at a cooling rate of 140° C./minute on average to form billets each having a diameter of 20 mm. Each billet was cold-drawn a plurality of times with intermediate annealing to produce a wire having a diameter of 0.5 mm and a length of 200 mm. Each of the resultant wires was heat-treated at 900° C. for 15 minutes, rapidly quenched by immersion in water with ice, and then subjected to an aging treatment by a heater shown in FIG. 1 for 15 minutes, to obtain a functionally graded alloy wire. The temperature distribution of the heater for the aging treatment is 140° C. in a low-aging temperature region and 300° C. in a high-aging temperature region, as shown in FIG. 2.

TABLE 1
Compositions of Functionally Graded Alloys
	Sample	Elements (weight %)
	No.	Cu	Al	Mn	Others
	1	Bal.	8.1	9.7	—
	2	Bal.	8.7	10.6	—
	3	Bal.	8.7	10.8	Ti: 0.1, B: 0.05
	4	Bal.	8.4	10.5	V: 0.26
	5	Bal.	7.6	9.7	V: 0.45
	6	Bal.	8.0	9.6	Ni: 1.0
	7	Bal.	8.1	9.7	Co: 0.5
	8	Bal.	8.0	9.5	Co: 2.4

[0140] Each wire thus aging-treated was measured with respect to properties described below in a low-aging temperature porrtion and a high-aging temperature portion to determine property gradient thereof.

[0141] (i) Hardness

[0142] The hardness of each wire was measured both in a low-aging temperature portion and a high-aging temperature protion by a micro-Vickers hardness tester. The measurement results are shown in Table 2.

[0143] (ii) Shape Recovery Ratio

[0144] Each wire was wound around a round rod having a diameter of 25 mm in liquid nitrogen, and measured with respect to a curvature radius R0 after taken out of the liquid nitrogen. The curved wire was then heated to 200° C. to recover its original shape, and again measured with respect to a curvature radius R1. The shape recovery ratio Rs of the wire was calculated by the formula: Rs(%)=100×(R1−R0)/R1. The calculated shape recovery ratios Rs are shown in Table 2.

[0145] (iii) Tensile Test

[0146] Each wire was subjected to a tensile test according to JIS Z 2241 to measure tensile strength, rupture elongation and yield strength (0.2% offset). The results are shown in Table 3.

TABLE 2
Hardness and Shape Recovery Ratio of Functionally
Graded Alloys
			Shape Recovery
	Hardness (Hv)		Ratio (%)
Sample No.	L*	H*	L*	H*
1	240	350	83	0
2	270	380	88	0
3	235	351	90	0
4	274	360	85	0
5	280	370	81	0
6	258	372	95	0
7	239	347	94	0
8	330	391	99	0
Note: *L: Low-aging temperature portion.
H: High-aging temperature portion.

[0147]

TABLE 3
Tensile Test Results of Functionally Graded Alloys
	Tensile Strength	Rupture	0.2% Offset Yield
	(MPa)	Elongation (%)	Strength (MPa)
Sample No.	L*	H*	L*	H*	L*	H*
1	432	1129	15.4	3.2	50	807
2	699	1074	17.2	3.3	310	774
3	639	728	15.7	3.2	315	544
4	749	1147	18.2	4.6	240	745
5	272	947	13.7	7.2	63	539
6	245	1032	18.2	2.7	212	783
7	529	894	17.3	3.6	237	717
8	594	650	2.4	0.0	370	Broken
Note:
*L: Low-aging temperature portion.
H: High-aging temperature portion.

[0148] As is clear from Tables 2 and 3, the properties are remarkably different between the low-aging temperature portion and the high-aging temperature portion. For example, Sample No. 1 exhibits yield stress (0.2% offset yield strength), which is as low as 50 MPa in a low-aging temperature portion and as high as 16 times or more in a high-aging temperature portion. In Sample No. 8 (Comparative Example 1) containing an excess amount of Co, the toughness of the high-aging temperature portion is remarkably deteriorated by the deposition of Co—Al, leading to breakage.

[0149] The wire of Sample No. 3 was divided into ten equal parts, and a center portion of each part was measured with respect to hardness. The results are plotted in FIG. 2. As is clear from FIG. 2, the hardness continuously increased from the low-aging temperature portion to the high-aging temperature portion. Particularly in the vicinity of the aging temperature of 250° C., the hardness drastically changed. It was confirmed from the change of hardness that a region extending up to about 7 cm from the low-aging temperature end had a crystal structure substantially composed of β-phase, and that a region extending up to about 7 cm from the high-aging temperature end had a dual-phase crystal structure composed essentially of an α-phase and a Heusler phase. In the intermediate region extending 6 cm between the low-aging temperature region and the high-aging temperature region, the crystal structure was gradually changing.

[0150] The wire of Sample No. 1 was observed by an optical microscope in both low-aging temperature portion and high-aging temperature portion. FIG. 3 is an optical photomicrograph showing the microstructure of the low-aging temperature portion of the functionally graded alloy of Sample NO. 1. As a result of electron diffraction analysis, it was confirmed that the crystal structure of the low-aging temperature portion was composed essentially of a β-phase. FIG. 4 is an optical photomicrograph showing the microstructure of high-aging temperature portion of the functionally graded alloy of Sample No. 1. It was also confirmed by electron diffraction that the microstructure of the high-aging temperature portion was a dual-phase structure of an β-phase and a Heusler phase.

[0151] As a result of X-ray diffraction analysis of Sample No. 1, it was confirmed that the low-aging temperature portion was composed of 100 volume % of a β-phase, with 0 volume % of an α-phase and a Heusler phase. It was also confirmed that the high-aging temperature portion was composed of 65 volume % of an α-phase and 35 volume % of a Heusler phase, with a β-phase substantially 0 volume %.

EXAMPLE 2

[0152] Copper-based alloys having compositions shown in Table 1 as Sample Nos. 2 and 3 were formed into wires each having a diameter of 0.5 mm and rapidly cooled in the same manner as in Example 1. The resultant copper-based alloy wires were then subjected to an aging treatment at 150° C., 200° C., 250° C., 300° C., 350° C. and 400° C., respectively, each for 15 minutes. The hardness of the aged copper-based alloy wires was measured in the same manner as in Example 1 and plotted in FIG. 5.

[0153] As is clear from FIG. 5, the hardness of the copper-based alloys rapidly increased when the aging temperature exceeded 250° C. However, the hardness of the copper-based alloys remarkably decreased when the aging temperature exceeded 350° C.

EXAMPLE 3

[0154] Copper-based alloys having compositions shown in Table 1 as Sample Nos. 5 and 6 were formed into wires each having a diameter of 0.5 mm and rapidly cooled in the same manner as in Example 1. The resultant copper-based alloy wires were subjected to an aging treatment at 300° C. for 5, 15, 60, 200, 700, 4500 and 10000 minutes, respectively. The hardness of the aged copper-based alloy wires was measured in the same manner as in Example 1 and plotted in FIG. 6.

[0155] As is clear from FIG. 6, in Sample No. 5 containing V and Sample No. 6 containing Ni, the highest hardness was obtained for an aging time of 5-700 times.

EXAMPLE 4

[0156] A copper-based alloy wire as shown in FIG. 7 was produced to provide a core wire 2 for a guide wire. The core wire 2 ha da total length of 1200 mm, and its tip end 4 was not tapered.

[0157] For this purpose, a copper-based alloy comprising 7.5 weight % of Al, 9.9 weight % of Mn, 2.0 weight % of Ni, and 80.6 weight % of Cu was melted, solidified at a cooling speed of 140° C./min. on average, and then cold-drawn to provide a wire of 0.4 mm in diameter. Thereafter, the wire was heat-treated at 900° C. for 10 minutes and rapidly quenched by immersion in ice water.

[0158] The resultant core wire 2 was cut to 1200 mm, and subjected to an aging treatment at different temperatures in four regions from the base end 3 to the top end 4 for 15 minutes; at 300° C. in a region 2a of 600 mm, at 250° C. in a region 2b of 300 mm, at 200° C. in a region 2c of 200 mm, and at 150° C. in a region 2d of 100 mm, respectively. With this heat treatment, the rigidity of the core wire 2 decreased from the based end 3 to the tip end 4. The hardness of each region was measured by a micro-Vickers hardness tester. The measurement results are shown in Table 4.

TABLE 4
Hardness distribution
Region Hardness (Hv)
2a     330
2b     290
2c     240
2d     235

[0159] It has been found that the Cu—at least—Mn alloy composing the core wire 2 can be provided with different properties at as small intervals as a few centimeters by heating conditions of the aging treatment. Thus, without tapering, a good balance of rigidity and softness can be achieved continuously along the core wire 2. Also, the core wire 2 is an integral wire made of an alloy of the same composition, which is excellent in torque conveyance.

EXAMPLE 5

[0160] A guide wire 11 was produced by using a copper-based alloy wire as shown in FIG. 10 as a core wire 12. The core wire 12 comprising four regions 12a (500 mm), 12b (100 mm), 12c (50 mm) and 12d (50 mm) from the base end 13 to the tip end 14 was tapered from region 12c to the tip end 14, such that regions 12a, 12b had a diameter of 0.4 mm, and that the tip end 14 had a diameter of 0.1 mm. The core wire 12 was subjected to the same aging treatment as in Example 4 under the following aging conditions: at 300° C. for region 12a, at 250° C. for region 12b, at 200° C. for region 12c, and at 150° C. for region 12d. The aging time was 15 minutes. With this aging treatment, the rigidity of the core wire 12 decreased from the base end 13 to the tip end 14.

[0161] The resultant core wire 12 was plated with gold, and coated with a polyamide elastomer layer 15 containing 40 weight % of barium sulfate as an X-ray contrast medium. Further, to improve lubrication at the time of insertion into the blood vessel, a surface of the coating layer 15 was covered by a lubricating layer 17 based on polyvinyl pyrrolidone.

EXAMPLE 6

[0162] A guide wire 21 as shown in FIG. 11 was produced. A core wire 22 comprising four regions 22a (500 mm), 22b (100 mm), 22c (50 mm) and 22d (50 mm) from the base end 23 to the tip end 24 was tapered from region 22c to the tip end 24, such that regions 22a, 22b had a diameter of 0.4 mm, and that the tip end 24 had a diameter of 0.1 mm. The core wire 22 was subjected to the same aging treatment as in Example 4 under the following aging conditions: at 300° C. for region 22a, at 250° C. for region 22b, at 200° C. for region 22c, and at 150° C. for region 22d. The aging time was 15 minutes. With this aging treatment, the rigidity of the core wire 22 decreased from the base end 23 to the tip end 24.

[0163] The tapered portion of the resultant core wire was covered by a coil 26, and the tip end 24 was provided with a expanded portion 27 by a plasma welding to avoid damaging of the blood vessel walls. The core wire 22 and the coil 26 were plated with gold. To improve lubrication at the time of insertion into the blood vessel, a surface of the gold plating was covered by a lubricating layer (not shown) based on polyvinyl pyrrolidone.

EXAMPLE 7

[0164] A core wire 32 of a guide wire 31 as shown in FIG. 12 was a braided wire made of three thin copper-based alloy wires. See FIG. 13, an A-B cross section of FIG. 12. The core wire 32 had rigidity stepwise decreasing along a region 32a (500 mm), a region 32b (100 mm) and a region 32c (50 mm) from the base end 33 to the tip end 34. The core wire 32 was tapered from region 32c to the tip end 34, such that a diameter was 0.4 mm in regions 32a, 32b and 0.1 mm at the tip end 34. The tip end 34 was provided with an expanded portion 36 by a plasma welding to avoid loosening of the braided wires and to improve the X-ray contrast of the tip end 34.

[0165] The core wire 32 was subjected to the same aging treatment as in Example 4 except for the following aging conditions: at 300° C. for region 32a, at 250° C. for region 32b, and at 200° C. for region 32c. The aging time was 15 minutes. With this aging treatment, the rigidity of the core wire 32 decreased from the base end 33 to the tip end 34.

[0166] The resultant core wire 32 was coated with a polyamide elastomer layer 35 containing 40 weight % of barium sulfate as an X-ray contrast medium. Further, to improve lubrication at the time of insertion into the blood vessel, a surface of the coating layer 35 was covered by a lubricating layer (not shown) based on polymethyl vinyl ether-maleic anhydride derivative.

EXAMPLE 8

[0167] A catheter as shown in FIG. 14 and 15 was produced. The catheter 41 comprised a superelastic Cu—Al—Mn alloy pipe 42 having an outer diameter of 1.5 mm and an inner diameter of 1.4 mm. The pipe 42 had a bending modulus decreasing stepwise from a body portion 42a to a tip end portion 42c through an intermediate portion 42b, and the tip end portion 42c became gradually softer toward the tip end 44.

[0168] For this purpose, a copper-based alloy comprising 7.5 weight % of Al, 9,9 weight % of Mn, 2.0 weight % of Ni, and 80.6 weight % of Cu was melted, solidified at a cooling speed of 140° C./min. on average, and then cold-rolled to provide a pipe of 2 mm in diameter and 0.1 mm in thickness. Thereafter, the pipe was heat-treated at 900° C. for 10 minutes and rapidly quenched by immersion in ice water.

[0169] The resultant pipe 42 was subjected to an aging treatment at different temperatures in three regions for 15 minutes; at 300° C. in a region 42a, at 250° C. in a region 42b, and at a temperature gradually decreasing from 200° C. to 150° C. in a region 42b, and at a temperature gradually decreasing from 200° C. to 150° C. in a region 42c, respectively. The pipe 42 was coated with a polyamide elastomer layer 46 containing 40 weight % of barium sulfate as an X-ray contrast medium and then with a polyvinyl pyrrolidone-based lubricating layer (not shown).

[0170] The resultant catheter 41 was rigid in a body portion 42a and fully soft in a tip end portion 42c, making sure safe use for practical applications. It is also possible to improve softness in the tip end portion 42c without tapering. Particularly in a microcatheter having a small diameter, its inner bore can be made relatively large, ensuring easy and safe injection of X-ray contrasting medium, etc.

EXAMPLE 9

[0171] A catheter as shown in FIGS. 16-18 was produced. The catheter 51 was constituted by a superelastic Cu—Al—Mn—V alloy pipe 52 having an outer diameter of 1.5 mm and an inner diameter of 1.4 mm. The pipe 52 had bending modulus decreasing stepwise from a body portion 52a to a tip end portion 52c through an intermediate portion 52b, and the tip end portion 52c was tapered such that it became gradually softer toward the tip end.

[0172] For this purpose, a copper-based alloy comprising 7.5 weight % of Al, 9.9 wieght % of Mn, 2.0 weight % of V, and 80.6 weight % of Cu was melted, solidified at a cooling speed of 140° C./min. on average, and then cold-rolled to provide a pipe of 2 mm in diameter and 0.1 mm in thickness. Thereafter, the pipe was heat-treated at 900° C. for 10 minutes and rapidly quenched by immersion in ice water.

[0173] The resultant pipe 52 was subjected to an aging treatment at different temperatures in three regions for 15 minutes; at 300° C. in a region 52a, at 250° C. in a region 52b, and at 150° C. in a region 52c, respectively. The pipe 52 was then coated with a polyamide elastomer layer 56 containing 40 weight % of barium sulfate as an X-ray contrast medium. The pipe 52 was provided with a soft tip 54 at the tip end to prevent the blood vessel walls from being damaged at the time of insertion. Like in Example 8, the pipe 52 was coated with a polyvinyl pyrrolidone-based lubricating layer (not shown) from the intermediate portion 52b to the tip end to increase lubrication at the time of insertion into the blood vessel.

[0174] The resultant catheter 51 was rigid in the body portion 52a and fully soft in the tip end portion 52c, making sure safe use for practical applications. Because this catheter 51 has properties changing from the body portion 52a to the tip end portion 52c, and because the tip end portion 52c is tapered toward the tip end, it has wide versatility in design with a rigid body portion and a soft tip end portion.

EXAMPLE 10

[0175] A catheter as shown in FIG. 19 was produced in the same manner as in Example 9. The catheter 61 was the same as in Example 9 except that a tip end portion 62 of the catheter 61 was bent at about 120°, This catheter 61 could easily be inserted into winding or branched blood vessels.

EXAMPLE 11

[0176] A PTCA catheter 71 equipped with a balloon as shown in FIGS. 20-22 was produced from the same Cu—Al—Mn—Ni alloy as in Example 8 in the same manner as in Example 9. The catheter 71 comprised a Cu—Al—Mn—Ni alloy pipe 72 having a diameter of 2 mm and a thickness of 0.1 mm. The pipe 72 had rigidity decreasing stepwise from a body portion 72a to a tip end portion 72c through an intermediate portion 72b, and the tip end portion 72c was tapered to become gradually softer toward the tip end.

[0177] The resultant pipe 72 was plated with gold and covered by a polyamide elastomer tube 73 in the tip end portion 72. The elastomer tube 73 had a through-hole 76 for allowing a balloon 75 to inflate, and a through-hole 77 extending from a halfway of the catheter 71 to the tip end portion for allowing a guide wire to pass through. Because the Cu—Al—Mn alloy pipe 72 extends almost up to a balloon region along the catheter 71, the catheter 71 has full rigidity while showing excellent softness and kink resistance, ensuring safe use.

EXAMPLE 12

[0178] A catheter as shown in FIGS. 23 and 24 was produced. The catheter 101 was constituted by a tube body 111, a hub 112 mounted to a base end of the tube body 111, and a soft tip 113 mounted to a tip end of the tube body 111. The tube body 111 was constituted by an inner layer 114, an intermediate Cu—Al—Mn alloy braid layer 115, and an outer layer 116 as shown in FIG. 24. The intermediate Cu—Al—Mn alloy braid 115 was made of eight 0.035-mm-thick Cu—Al—Mn alloy wires comprising 7.5 weight % of Al, 9.9 weight % of Mn, 2.0 weight % of Ni, and 80.6 weight % of Cu. The thin Cu—Al—Mn alloy wires were produced in the same manner as in Example 9 The Cu—Al—Mn alloy braid 115 was coextruded with nylon 12 to form the catheter 101 having the Cu—Al—Mn alloy braid 115 embedded in the tube body 111.

EXAMPLE 13

[0179] A catheter as shown in FIGS. 25 and 26 was produced. The catheter 102 comprised a tube body 121, a hub 122 mounted to a base end of the tube body 121, and soft tip 123 mounted to a tip end of the tube body 121. The tube body 121 comprised an inner layer 124, an intermediate Cu—Al—Mn alloy braid layer 125, and an outer layer 126 as shown in FIG. 26. The intermediate Cu—Al—Mn—V alloy braid 125 comprised 32 thin Cu—Al—Mn—V alloy wires having a thickness of 0.02 mm comprising 8.0 weight % of Al, 10.2 weight % of Mn, 1.0 weight % of V, and 80.8 weight % of Cu. The Cu—Al—Mn—V alloy braid 125 was subjected to an aging treatment at 300° C. in a region a, at 250° C. in a region b and at 150° C. in a region c for 15 minutes, so that the regions a, b and c had rigidity decreasing in this order. The Cu—Al—Mn—V alloy braid 115 was coextruded with a polyurethane resin in the same manner as in Example 12 to form a catheter 102 having the Cu—Al—Mn—V alloy braid 125 embedded in the tube body 121.

EXAMPLE 14

[0180] A catheter as shown in FIGS. 27 and 28 was produced. The catheter 103 comprised a tube body 131, a hub 132 mounted to a base end of the tube body 131, and a soft tip 133 mounted to a tip end of the tube body 131. The tube body 131 comprised an inner layer 134, an intermediate Cu—Al—Mn—V alloy braid layer 135, and an outer layer 136 as shown in FIG. 28. The intermediate Cu—Al—Mn—V alloy braid 135 comprised two spirally crossing Cu—Al—Mn—V alloy ribbons each having a thickness of 0.01 mm comprising 8.0 weight % of Al, 10.2 weight % of Mn, 1.0 weight % of V, and 80.8 weight % of Cu. The Cu—Al—Mn—V alloy braid 135 was subjected to an aging treatment at temperatures shown in Table 5 below for 15 minutes so that regions d, e, f and g had rigidity decreasing in this order. The hardness of the braid 135 in each region was measured by a micro-Vickers hardness tester. The measurement results are shown in Table 5.

	TABLE 5
	Region	Aging Temperature (° C.)	Hardness (Hv)
	d	300	380
	e	250	290
	f	200	260
	g	150	270

[0181] The Cu—Al—Mn—V alloy braid 135 was coextruded with nylon 12 in the same manner as in Example 12 to form a catheter 103 having the Cu—Al—Mn—V alloy braid 135 embedded in the tube body 131.

EXAMPLE 15

[0182] A catheter as shown in FIGS. 29 and 30 was produced. The catheter 104 comprised a tube body 141, a hub 142 mounted to a base end of the tube body 141, and a soft tip 143 mounted to a tip end of the tube body 141. The tube body 141 comprised an inner layer 144, four intermediate wires 145 made of the same Cu—Al—Mn—V alloy as in Example 13, and an outer layer 146. The Cu—Al—Mn—V alloy wires 143 were subjected to an aging treatment at 300° C. in a region h, at 250° C. in a region i and at 150° C. in a region j for 15 minutes, so that the regions h, i and j had rigidity decreasing stepwise in this order. Also, the catheter 104 was tapered from a halfway of the region i to the tip end to ensure softness.

EXAMPLE 16

[0183] A catheter as shown in FIGS. 31 and 32 was produced in the same manner as in Example 13. The catheter comprised a tube body 152, a Y-shaped hub 152 mounted to a base end of the tube body 151, and a balloon 154 mounted to a tip end of the tube body 151. The tube body 151 had a hole 157 for inflating the balloon 154, a thin Cu—Al—Mn alloy wire 155 and an outer layer 156. The Cu—Al—Mn alloy wire 155 was subjected to an aging treatment at 300° C. in region k, at 250° C. in region 1 and at 150° C. in region m for 15 minutes, so that regions k, 1 and m had rigidity decreasing stepwise in this order. Also, the catheter 105 was tapered from a halfway of region m to the tip end to ensure softness.

[0184] As described above in detail, the functionally graded alloy of the present invention exhibits drastically changing properties such as shape recovery properties, superelasticity, hardness, mechanical strength, etc., without mechanical working such as cutting or chemical treatment such as etching for imparting size gradient. Such a functionally graded alloy can be easily produced at low cost from a copper-based alloy composed essentially of a β-phase, by aging treatment in a heater having a continuous or stepwise temperature gradient. The functionally graded alloy of the present invention can be formed into various shapes because of its excellent cold workability.

[0185] When the core wire, the guide wire or the catheter comprises a copper-based alloy having gradient properties according to the present invention, it is provided with optimum rigidity and toughness in the body portion and proper softness in the tip end portion without mechanical or chemical working. Such core wire, guide wire or catheter is excellent in insertion operability and torque conveyance, and can be inserted and placed at a desired spot in the blood vessel without damaging the walls thereof.

Claims

1. A core wire for a guide wire comprising a body portion having a high rigidity and a tip end portion having a rigidity lower than the rigidity of the body portion, wherein at least part of said core wire is made of a copper-based alloy comprising 3-10 weight % of Al and 5-20 weight % of Mn, the balance being substantially Cu and inevitable impurities.

2. The core wire for a guide wire according to claim 1 wherein said copper-based alloy wire is formed by at least one of hot-working and cold-working, maintained at a temperature of at least 500° C. and rapidly quenched, and then aged at a temperature of not more than 200° C. such that the core wire has shape recovery properties and superelasticity.

3. The core wire for a guide wire according to claim 1 wherein said copper-based alloy wire comprises a high-rigidity body portion, a low-rigidity tip end portion, and an intermediate portion between said high-rigidity body portion and said low-rigidity tip end portion, said intermediate portion having rigidity continuously or stepwise decreasing from said high-rigidity body portion to said low-rigidity tip end portion.

4. The core wire for a guide wire according to claim 1 wherein said copper-based alloy wire is formed by hot working and cold working, maintained at a temperature of at least 500° C. and then rapidly quenched, and further subjected to an aging treatment comprising heating the high-rigidity body portion at a temperature of 250-350° C., heating the tip end portion at a temperature of less than 250° C., and an intermediate portion, and heating an intermediate portion between said body portion and said tip end portion at a temperature continuously or stepwise changing from the heating temperature of said body portion to the heating temperature of the tip end portion.

5. A guide wire comprising the core wire according to claim 1.

6. The guide wire according to claim 5 wherein said core wire is coated with a coating selected from the group consisting of Au, Pt, Ti, Pd, and TiN, and optionally with a resin.

7. A catheter at least partially comprising a metal pipe, said metal pipe being made in at least a tip end portion thereof of a copper-based alloy comprising 3-10 weight % Al and 5-20 weight % Mn, the balance being substantially Cu and inevitable impurities.

8. The catheter according to claim 7 wherein said metal pipe has a bending modulus which decreases continuously or stepwise in a direction from a base end to a tip end of the catheter.

9. The catheter according to claim 7 wherein said metal pipe is formed by at least one of hot working and cold working, maintained at a temperature of at least 500° C. and rapidly quenched, and then subjected to an aging treatment at a temperature distribution that decreases continuously or stepwise in a direction from a base end to a tip end of the catheter, wherein the highest temperature is 250-350° C. and the lowest temperature is less than 250° C. in said temperature distribution.

10. The catheter according to claim 7 wherein said metal pipe has an outer diameter which is at least partially decreasing continuously or stepwise in a direction from a base end to a tip end of said catheter.

11. The catheter according to claim 7 wherein said metal pipe is coated with a coating selected from the group consisting of Au, Pt, Ti, Pd, and TIN and optionally a resin.

12. A catheter containing a reinforcing metal member in at least part of a catheter tube, said reinforcing metal member being made of a copper-based alloy comprising 3-10 weight % Al and 5-20 weight % Mn, the balance being substantially Cu and inevitable impurities.

13. The catheter according to claim 12 wherein said reinforcing metal member has a bending modulus which decreases continuously or stepwise in a direction from a base end to a tip end of the catheter.

14. The catheter according to claim 12 wherein said reinforcing metal member is formed by at least one of hot working and cold working, maintained at a temperature of at least 500° C. and then rapidly quenched, and then subjected to an aging treatment at such a temperature distribution that decreases continuously or stepwise in a direction from a base end to a tip end of said catheter, wherein the highest temperature in the temperature distribution is 250-350° C. and the lowest temperature in the temperature distribution is less than 250° C.

15. The catheter according to claim 12 wherein said reinforcing metal member is at least one thin copper-based alloy wire extending along said catheter.

16. The catheter according to claim 12 wherein said reinforcing metal member is a braid of thin copper-based alloy wires.

17. The catheter according to claim 12 wherein said reinforcing metal member is a coil of a thin copper-based alloy wire.