Patent Grant
8652199
This invention relates to a stent to be placed in a lumen of a human body or an animal.
As well known, a shape memory alloy, such as a Ti—Ni alloy, exhibits a remarkable shape memory effect in association with martensitic reverse transformation and exhibits spontaneous shape recovery and excellent spring characteristics (superelasticity) in a parent phase region after the reverse transformation from a martensite region. The superelasticity is observed in a number of shape memory alloys and, among others, is particularly remarkable in the Ti—Ni alloy and a Ti—Ni—X alloy (X=V, Cr, Co, Nb, or the like).
The shape memory effect of the Ti—Ni alloy is described in Patent Document 1. The superelasticity of the Ti—Ni alloy is described in Patent Document 2.
On the other hand, the shape memory effect and the superelasticity of the Ti—Ni—X alloy are described, for example, in Patent Documents 3 and 4 for a Ti—Ni—V alloy and in Patent Document 5 for a Ti—Ni—Nb alloy.
As compared with the Ti—Ni alloy, the Ti—Ni—Nb alloy used in this invention exhibits a characteristic that temperature hysteresis of stresses is increased by applying a stress. Therefore, the Ti—Ni—Nb alloy is put into practical use as a joint for reactor piping.
Stent treatment is a new technique rapidly put into use in recent years. The stent is a mesh-like metal tube to be placed in a living body in order to prevent renarrowing or restenosis of a narrow portion, such as a blood vessel, after it is expanded. The stent is reduced in diameter and received in an end portion of a catheter. After introduced into the narrow portion, the stent is released from the catheter and expanded to be attached to an inner wall of a lumen such as a blood vessel.
In case of PTCA (percutaneous transluminal coronary angioplasty), the stent is expanded following a blood vessel expanding operation by inflation of a balloon set on an inner wall for housing. The stent is called a balloon expandable stent and formed by the use of a metal such as stainless steel or tantalum.
On the other hand, in order to prevent rupture of an aneurysm which may result in a subarachnoid hemorrhage or the like, blood supply to the aneurysm is stopped. As one of such techniques, use is made of embolization in which a metal coil, such as a platinum coil, is implanted into the aneurysm so as to form a blood clot. However, it is pointed out that a part of the blood clot may possibly be released from the metal and carried by a bloodstream to a periphery to block a blood vessel. In order to avoid this, consideration is made about a covered stent technique in which the aneurysm is embolized by the use of a graft. In this case, simultaneously when the stent is released from the catheter, the stent is expanded by its own spring function to press the graft against a blood vessel wall. Such stent is called a self expandable stent. For the self expandable stent, a material having an excellent spring characteristic is desired.
The Ti—Ni shape memory alloy is characterized in that, at a temperature above a reverse transformation finish temperature (Af point) at which reverse transformation of the alloy starting from a reverse transformation start temperature (As point) is finished, the alloy which has been deformed under an external load is recovered into an original shape simultaneously when the external load is released and that recoverable deformation reaches about 7% in case of an elongation strain. Herein, the As point means a shape recovery start temperature while the Af point means a shape recovery finish temperature (shape recovery temperature). For use as the stent, a hoop-shaped stent is formed into a size slightly greater than the lumen where the stent is to be placed. The stent is reduced in diameter and mounted to the catheter. Simultaneously when the stent is released from the catheter, the stent is spontaneously recovered into its original diameter to be brought into tight contact with the lumen. Thus, the alloy has the Af point not lower than a living body temperature (around 37° C.). As well as the above-mentioned merits, such superelastic stent has several demerits, such as occurrence of damage in the blood vessel wall, a positioning error in placement, lack in deliverability, and so on due to its spontaneous shape recovery characteristic. Therefore, it is difficult to use the superelastic stent in a blood vessel system such as a coronary system.
The stent for PTCA is preferably made of a metal material having a low elastic limit, which hardly damages the blood vessel and is excellent in deliverability. However, there is left a problem that a pressing force (expanding force) against a lumen wall after expansion is weak. As means to solve the problem, a stent using a shape memory alloy is proposed. Patent Document 6 describes that a Ti—Ni—Nb alloy, which is a material similar to that used in this invention, is applied to a stent. This document describes that the stent made of a Ti—Ni—Nb shape memory alloy and having a low Young's modulus upon shape recovery and a high Young's modulus upon shape deformation under an external load is obtained when the ratio of stress on loading to the stress on unloading at the respective inflection points on a stress-strain curve in alloy deformation is at least about 2.5:1. This stent exhibits superelasticity at the living body temperature after it is released from the catheter but does not sufficiently solve the above-mentioned problem (arbitrariness in positioning) as required in PTCA.
In Patent Document 7, the present inventors have proposed a stent closely related to this invention. Specifically, proposal is made of the stent which exhibits no shape memory at the living body temperature during insertion into the living body and exhibits superelasticity after shape recovery by inflation of a balloon. In the embodiment, it is described that the stent made of a Ti—Ni alloy or a Ti—Ni—X alloy (X=Cr, V, Cu, Fe, Co, or the like) is subjected to strong deformation to thereby elevate a recovery temperature. However, this document does not refer to a graded function of the stent. Further, a strain is given only by strong deformation of a slotted stent received in the catheter. Depending upon a slot shape, a sufficient effect is not obtained. Patent Document 8 discloses a stent using a Ti—Ni alloy or a Ti—Ni—X alloy and proposes to partly change the stiffness of the material by heat treatment. Specifically, such change by heat treatment provides a series of superelastic portions having a relatively high stiffness and plastically deformable portions having a relatively low stiffness (in the description, portions where the superelasticity is destroyed) which are alternately arranged. Thus, this technique is different in gist and means intended by this invention.
The stent is required to have functions such as deliverability (accessibility to peripheral or distal parts), prevention of restenosis (strong expanding force after placement), and flexible shape conformability. Following recent increase in stent treatment cases, a problem of restenosis after placement of the stent is exposed.
For example, in case where the stent is placed at a tortuous coronary artery lesion, a restenotic lesion after placement tends to occur at opposite ends of the stent which are most susceptible to stimulation. In this event, re-placement of the stent or bypass surgery must be performed so that mental and physical burdens on a patient are extremely heavy. The deliverability (accessibility to peripheral parts) during operation is achieved by using a stainless steel material. The strong expanding force after placement is achieved by a conventional Ti—Ni—X alloy superelastic material. In order to achieve the flexible shape conformability (relaxation of stimulation to the restenotic lesion) after placement, it is proposed to weaken the expanding force of the stent to relax the stimulation to the lumen. However, this results in loss of an inherent function (reinforcement of the lumen) of the stent. Practically, a material-based approach is difficult. Therefore, at present, stent processing such as designing of a slot shape is relied upon as secondary means. However, various essential problems are left unsolved.
Patent Document 1: U.S. Pat. No. 3,174,851
Patent Document 2: JP S58-161753 A
Patent Document 3: JP S63-171844 A
Patent Document 4: JP S63-14834 A
Patent Document 5: U.S. Pat. No. 4,770,725
Patent Document 6: JP H11-42283 A
Patent Document 7: JP H11-99207 A
Patent Document 8: JP 2003-505194 A
It is therefore a technical object of this invention to provide a stent which holds various performances such as deliverability (accessibility to peripheral parts), prevention of restenosis (strong expanding force after placement), flexible shape conformability, and so on and is therefore adaptable not only to a bile duct but also to a blood vessel system such as a tortuous coronary artery substantially without causing restenosis.
According to this invention, there is provided a stent made of a Ti—Ni based shape memory alloy as a material, the stent having at least one parent phase region and at least one martensite region or two or more parent phase regions different in shape recovery temperature arranged along its lengthwise direction so that a tensile strength in the lengthwise direction is varied. The stent holds a part or all of the above-mentioned performances by automatically adjusting a function during operation and placement.
The Ti—Ni based shape memory alloy used in this invention is a shape memory alloy containing titanium (Ti) and nickel (Ni) as essential components, for example, a Ti—Ni alloy or a Ti—Ni—X alloy (herein, X being an element such as Fe, V, Cr, Vo, Nb, or the like).
In this invention, by providing the martensite region occupying ⅔ or more (preferably ⅘ or more) of the total length, it is possible to provide a stent which is, as a stent function during operation, excellent in operability and suppressed in risk of damaging a lumen wall due to spontaneous shape recovery. Further, by providing the parent phase region at the center portion in the lengthwise direction, it is possible to provide a stent which is, as a stent function during placement, excellent in expanding force.
Further, in this invention, by providing the parent phase region at the center portion of the lengthwise direction and, at opposite ends, the martensite regions or the parent phase regions smaller in expanding force than the center portion, it is possible to provide a stent excellent in shape conformability.
According to this invention, it is possible to provide a stent which hardly causes a restenosis lesion not only in a blood vessel of a human body or an animal but also in various kinds of lumens and which is readily operable.
Now, an embodiment of this invention will be described. In the following description, an alloy wire rod or simply a wire rod refers to an alloy material or a material in the form of a hollow thin wire.
(a) At first, a heat-treatment effect will be described.
By high-frequency melting, hot working, and cold working, a hollow wire rod was obtained which was made of a Ti-51 at % Ni alloy, formed into a tube having an outer diameter of ø2 mm and a thickness of 0.15 mm, and reduced in diameter to ø1 mm. The tube was subjected to laser machining and thereafter expanded into ø5 mm to obtain a stent illustrated in
Next, the stent was, over its entire length, subjected to aging at 400° C. for 50 hours. Thereafter, one sample was, only at the center of the stent, subjected to heat treatment again at 500° C. for 5 minutes. Another sample was similarly subjected to heat treatment again at 700° C. for 0.5 minute.
a) and (b) show stress-strain curves at 37° C. for heat-treated test samples of the above-mentioned wire rods having a diameter of ø1 mm. It is understood that the aged material in
The shape recovery temperature of the stent using the tube is obtained by reducing the diameter into ø2 mm in a dry ice alcohol bath (at about −50° C.) and then gradually heating the stent. It has been confirmed that characteristics of respective portions at 37° C. are similar to those in (a) and (b) of
The amount of self recovery of the center portion of the stent after it is released from a catheter can be selected by the length of the parent phase region in the length of the stent and the strength of recovery. In this example, with the treatment at 500° C., self recovery of the center portion of the stent was observed in case where the parent phase region was shorter than ⅘ of the stent length. However, with the treatment at 700° C., the recovery of the center portion could be suppressed when the parent phase region was shorter than ⅔ of the stent length. The opposite end portions as the martensite regions and the unrecovered center portion were recovered into the original stent shape by balloon expansion. From the above, it has been revealed that, by selecting heat-treatment conditions and heat-treatment zones, necessity or unnecessity of balloon expansion at the living body temperature and the change in tensile strength after placement in the stent length direction can be achieved as desired.
It is known that the change in transformation temperature of the alloy is obtained by appearance of an R phase caused by aging in case of an Ni-excess Ti—Ni alloy and a Ti—Ni—X alloy with Fe, V, Co, Cr, Nb, or the like added and obtained by aging after strong deformation (thermomechanical treatment) in case of all kinds of Ti—Ni alloy and the Ti—Ni—X alloy exhibiting a shape memory effect. A superelastic recovering force in the parent phase region is obtained as ΔT (=measurement temperature−Af temperature) is greater and the density of deformation texture in the alloy is higher. In this case also, functionality was considered about various kinds of alloys such as a Ti-50 at % Ni alloy, a Ti-49 at % Ni-1 at % V alloy, and a Ti-48 at % Ni-3 at % Nb alloy. As a result, by appropriately selecting the working conditions and the heat-treatment conditions, the effect of this invention could be obtained. For example, in case of the Ti-50 at % Ni alloy, a slotted tube having a diameter of ø2 mm is expanded into ø5 mm by strong deformation. Thereafter, only opposite end portions are heated at 600° C. in a short time (1 to 2 seconds). Thus, the stent is obtained which is superelastic at the center portion (parent phase region) and which has the martensite regions at the opposite end portions and is different in function in the lengthwise direction.
(b) Next, a prestrain effect will be described.
As shown by Nos. 1, 2, and 3 in Table 1, wire rods made of Ti-51 at % Ni, Ti-49 at % Ni-3 at % Nb, and Ti-47.5 at % Ni-6 at % Nb alloys and having a diameter of ø1 mm with a cold working rate of 30% were heat-treated at 400° C. for one hour. The relationship between the applied strain (applied at a temperature not higher than the As point) and the shape recovery temperature was examined for each sample. The result is shown in Table 1 also.
The alloy No. 1 shown in Table 1 had a shape recovery temperature of 20° C. at a strain (ε)=0%, a shape recovery temperature of 20° C. at ε=8%, a shape recovery temperature of 25° C. at ε=10%, a shape recovery temperature of 30° C. at ε=13%, and a shape recovery temperature of 30° C. at ε=15%.
The alloy No. 2 had a shape recovery temperature of 10° C. at ε=0%, a shape recovery temperature of 12° C. at ε=8%, a shape recovery temperature of 25° C. at ε=13%, and a shape recovery temperature of 30° C. at ε=15%.
The alloy No. 3 had a shape recovery temperature of 18° C. at ε=0%, a shape recovery temperature of 23° C. at ε=8%, a shape recovery temperature of 28° C. at ε=10%, and a shape recovery temperature of 50° C. at ε=15%.
In each of the alloys Nos. 1, 2, and 3, an increase in shape recovery temperature by prestrain is observed. In particular, this effect is remarkable in the 6 at % Nb-added alloy as the sample No. 3. It has been found out that, by adjusting the applied strain, the stent function can be changed in the lengthwise direction. For example, the applied strain is 10% at the center portion of the stent and 13% at the opposite end portions, the shape recovery temperature of the stent exceeds the living body temperature. Therefore, the deliverability during operation is assured. By heating (at 42° C.) after placement, the entire length of the stent is transformed into the parent phase region and the expanding force at the center portion can be increased. Alternatively, it is possible to provide a stent in which only the end portions are applied with the strain of 13% or more to be transformed into the martensite regions. Further, in the sample No. 1 alloy and the sample No. 2 alloy also, the shape recovery temperature during heat treatment is controlled by aging or thermomechanical treatment so that the change in stent function by prestrain can be made like in the sample No. 3 alloy. Thus, the effect of this invention can be obtained.
Next, a tapered wedge was inserted into a slotted tube of the Ti-46.5 at % Ni-6 at % Nb alloy as the sample No. 3 having a diameter of ø2 mm. As shown in
(c) Next, the heat treatment and the prestrain effect will be described.
The Ti—Ni shape memory alloy has a yield stress depending upon the temperature. In the superelasticity at the living body temperature also, the yield stress is higher and the expanding force is greater as the shape recovery temperature is lower. In this example, by the use of the sample No. 3 alloy mentioned above, the stent was prepared under the conditions shown in Table 2. Specifically, the entire length of the stent was heat treated at 400° C. Thereafter, the opposite end portions alone were heat treated at about 525° C. Thereafter, in the above-mentioned manner, required strains ε=13% and ε=8% were applied. After heating to 42° C., the stent function was examined. As a result, the change in expanding force at 37° C. was observed.
(d) Next, the applicability will be described.
Herein, the operability of the stent was verified by the use of a swine blood vessel. The stent exhibiting a shape recovery temperature higher than 37° C. as an example of this invention exhibited smooth deliverability for the tortuous blood vessel and arbitrariness of placement to lesions. Physiologic saline for use in a balloon expanding operation after placement was kept at 45° C. and used to heat the stent. As a result, the stent holds desired functions (having the martensite region partially and the parent phase region partially, or entirely having the parent phase region with variation in expanding force).
As described above, according to this invention, desired stent characteristics depending upon the condition of the lesions can be achieved by material design although this approach have been difficult so far. It is possible to achieve a new design of the stent.
Alloys applicable to this invention include a Ti—Ni based alloy exhibiting a shape memory effect and a Ti—Ni—X alloy containing third and fourth elements such as Fe, Cr, V, Co, Nb and so on.
A suitable alloy in this invention using the heat treatment effect is an Ni-excess alloy, such as a Ti-51 at % Ni alloy, easy in appearance of an R phase by aging. A suitable alloy using the prestrain effect is a Ti—Ni—Nb alloy and the content of Nb is 3 at % or more exhibiting a remarkable effect of addition. Excessive addition degrades workability of the alloy. Preferably, the content is 6 to 9 at %.
As described above, the stent according to this invention is most suitable as a stent with an autonomic function excellent in deliverability, expanding force, and shape conformability and autonomously adaptable to lesions in a living lumen.
| Number | Date | Country | Kind |
|---|---|---|---|
| 2005-148995 | May 2005 | JP | national |
| Filing Document | Filing Date | Country | Kind | 371c Date |
|---|---|---|---|---|
| PCT/JP2006/310197 | 5/23/2006 | WO | 00 | 2/5/2008 |
| Publishing Document | Publishing Date | Country | Kind |
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| WO2006/126513 | 11/30/2006 | WO | A |
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