CA1115455A - Inherent shape memory coupling for heart valve - Google Patents
Inherent shape memory coupling for heart valveInfo
- Publication number
- CA1115455A CA1115455A CA327,878A CA327878A CA1115455A CA 1115455 A CA1115455 A CA 1115455A CA 327878 A CA327878 A CA 327878A CA 1115455 A CA1115455 A CA 1115455A
- Authority
- CA
- Canada
- Prior art keywords
- coupling element
- temperature
- heart valve
- transition
- ring
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
- A61L27/507—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials for artificial blood vessels
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/24—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
- A61F2/2403—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body with pivoting rigid closure members
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/02—Inorganic materials
- A61L27/04—Metals or alloys
- A61L27/047—Other specific metals or alloys not covered by A61L27/042 - A61L27/045 or A61L27/06
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2400/00—Materials characterised by their function or physical properties
- A61L2400/16—Materials with shape-memory or superelastic properties
Abstract
ABSTRACT
A prosthetic heart valve for long-term implantation in the human body is made by using a coupling element to join a circumscribing sewing cuff to a generally tubular, rigid portion of a heart valve body. A ductile metal alloy coupling element at a temperature below its transition temperature is deformed from its original shape. Heating the coupling element to a temperature above the transition temperature, as by passing electric current therethrough, causes the coupling to try to return to its original shape and effects a secure joinder.
A prosthetic heart valve for long-term implantation in the human body is made by using a coupling element to join a circumscribing sewing cuff to a generally tubular, rigid portion of a heart valve body. A ductile metal alloy coupling element at a temperature below its transition temperature is deformed from its original shape. Heating the coupling element to a temperature above the transition temperature, as by passing electric current therethrough, causes the coupling to try to return to its original shape and effects a secure joinder.
Description
lllS455 ,. PROSTHETIC DEVICE COUPLINGS
, .BACKGROUND OF THE INVENTION
This invention relates to prosthetic aevices and more particularly to prosthetic devices designed for long-term implantation in the human body wherein it is necessary to make a connection between two components or between~a prosthetic element and an element o~ the human body.
In fabricating prosthetic devices for implanta~
tion in the human body, it often becomes necessary to attach dissimilar materials to each other. One example is the attachment of a fabric sewing cuff to the ex-terior of a housing portion of a heart valve. Hereto-fore, such fabric sewing cuffs have been attached using a circumferential fabric wrapping, a heat-shrinkable synthetic polymer, or a wrapping of metallic wire. How-ever, because it is now hoped that heart valves andother such prosthetic devices, once implanted within the ~! human body, can stay there for the life of the patient, it is important that the joinder remain excellent over a long period of time. It is also desired to eliminate any possibility of failure as a result of mishandling in any ` way, as for example by overheating a heat-shrinkable ` polymer. Moreover, synthetic polymers are inherently -~ subject to creep over their lifetime, and if, for exam-ple, a heart valve should ever break loose from the sew-x- 25 mg cuff, the possible harm to the patient would be most serious.
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---` lllS4SS
- la -SUMMARY OF THE INVENTION
In a particular aspect, the invention provides a prosthetic heart valve for long term implantation in the human body including a generally tubular rigid por-tion, a circumscribing sewing ring disposed in encircling relationship to said rigid tubular portion, and a coupling element embedded within said sewing ring for joining said sewing ring to said heart valve tubular portion wherein the improvement comprises said coupling element being made of a nickel-titanium alloy having a transition-temperature range, said element having been formed to a precise shape at a temperature above said range and having been deformed to a different shape at a temperature below said range whereby joinder of said sewing ring to said rigid tubular portion is effected by raising the temperature of said element above said range in order to cause said alloy to attempt to return to said precise shape.
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`` ~115455 Accordingly, the present invention proyides a method for securely joining a prosthetic element to a natural element of the human bo~y or to another component of the prosthetic device itself. me invention utilizes a coupling element made from a metal alloy which has the novel property of, upon heating, returning to a precise shape from which it has been deformed at a lower temperature. Nickeltitanium alloys have been developed from appro-xImately equiatomic a~ounts of nickel and titanium, and these alloys have a transition-temperature range above which they exhibit an inherent shape memory.
Thus, by machining such an alloy to a precise shape desired for a particular prosthetic application, cooling the alloy below the transition-temperature range and deformlng the cooled alloy by expansion, contraction or bending, it will return to the precise original shape upon warming above the transition temperature. m e precision which such a metal alloy exhibits can be used to t important advantage in prosthetic applications.
BRIEF DESCRIPTION'OF'THE'DRAWINGS
~dvantages of the invention will be apparent from the following de-tailed description when read in conjunction with the appended drawings wherein:
FIGUR~ 1 is a perspective view of a heart valve having a sewing cuff attachel thereto in a manner embodying variGus features of the present in-vention;
i~ .
FIGURE 2 is a sectional view taken generally along line 2-2 of FIGURE 1 with the valve menber shown in the closed position;
FIGURE 3 is a perspective view of a blood access device where arti-~'~ ficial grafts are attached to the entry and exit ends thereof by coupling ele-- ments in accordance with the present invention.
i FIGURE 4 is a sectional view taken along line 4-4 of FIGURE 3;
- FIGURE 5 de nstrates the connection of an artificial tendon or liga-ment to a bone which is a part `
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. .
of a living body;
FIGURES 6A and 6B are enlarged fragmentary views illustrating the connection shown in FIGURE 5;
and FIGURE 7 is a fragmentary sectional view general-ly similar to FIGURE 2 showing another method of attach-ment`embodying various features of the present invention.
DESCRIPTION OF THE PREFERRED EMBODIMENTS
Illustrated in FIGURE 1 is a pivoting disc heart valve 11 designed for replacement of a defective valve in a human heart. The heart valve 11 includes a rigid housing or body portion 13 of g enerally tubular shape which has an essentially circular periphery. The housing 13 has a groove 15 formed in the exterior of its side wall. A sewing ring or cuff 17 is attached to the exterior, grooved portion of the side wall and permits the replacement valve 11 to be sutured in place.
The invention is equally applicable to heart valves of various different designs, for example a ball and cage type valve, although a pivoting disc valve is il-lustrated. A circular disc 19 serves as a valve member and pivots or rotates from an open position to a closed position and back to the open position in response to dif-ferential blood pressure. The disc 19 is retained on a shaft 21 which passes through apertures in a pair of support lugs 23. Thus, the disc is free to turn about - the shaft 21 as a pivot point:which is located as an off-center or eccentric axis with respect to the circular disc 19. The interior portion of the housing 13 is ap-39 propriately ta~ered so as to cooperate with the disc 19 in sealing the valve opening. The construction and opera-tion of the valve 11 is more particularly pointed out in U.S. Patent No. 3,546,711,issued December 15, 1970.
The fabric sewing ring 17 has an outer covering 25 of a suitable synthetic polymer fabric, prèferably a polyester, such as that sold under the trademark Dacron, ' . , - :, :
, ~1~5455 which is biocompatible. As seen in FIGURE 2, the sewing ring 17 has embedded therein a coupling element 27 made of a nickel-titanium alloy, and dis-posed exterior thereof there is provided a larger, generally soft ring 29 of a suitable synthetic plastic material, such as a fluorosilicone rubber or some similar semi-rigid polymer that is biocompatible and capable of sterilization.
` The coupling element 27 is made of a nickel-tita~ium alloy of the type marketed under the trademarkNitinol by RayChem, Co. These metal alloys, contain-ing about 50 percent atoms of nickel and about 50 percent atoms of titanium, have a transition-tempera-ture range above which the alloy will return to a precise fabricated shape. Accordingly, the coupling ele-ment 27 is formed to the precise shape desired by molding, casting, machining or the like at a tempera-ture above the transition-temperature. The particular transition-temperature range is dependent upon the precise metallic composition of the alloyr and it can be varied in order to tailor the alloy to a particu-lar application. Such a change in transition-tempera-ture range is accomplished in either of two ways: by adding additional nickel in excess of the 50:50 ratio ;~ 25 or by substituting a particular atomic amount of cobalt for the same atomic amount of nickel. For a pros-thetic device, an alloy is preferably used which be-comes ductile at a temperature below normal body tem-- perature, i.e., at about 37C. or below although al-loys having a higher transition temperature may be `~ employed.
Below the transition-temperature range, these metallic alloys exhibit excellent ductility and may be deformed in an amount of up to 8 percent without inhibiting their ability to return to the precise origi-nal configuration. The strain which is introduced by ,. _ ~llS455 physical deformation at a temperature below the transition-temperature ran~e, is, in effect, a stora~e of energy, and when the alloy is heated to and through the temperature-transition range, the alloy quickly tries to return to its original shape. Consequently, the coupling element 27 becomes physically entrapped within the groove 15 in the sidewall of the housing from which it cannot escape. By forming the coupling element 27 to precise dimensionsl and similarly holding a close toler-ance on the exterior demension of the heart valve housing13, ti~e fabric covering 25 for the sewing ring is securely squeezed between the coupling element and the rigid grooved wall, and the sizilig may be such that the ring 27 cannotquite return and thus it will remain with a predetermined amount of tensile stress throughout. The alloy is rigid and unyielding above the transition-temperature range, and advantage can further be taken of this property to create a secure joinder.
After assembly of the coupling element-27and the fabric covering 25, the semi-rigid ring 29 is installed, and the fabric covering is then enveloped about it and sewn together at a suitable circular seam using standard techniques. This metallurgically homogeneous coupling element 27 joins the sewin~ ring 17 to the valve body 13 in so secure a manner that there is no reasonable chance of the ring 17 parting from the housin~ 13 even after years of implantation in the body of the patient.
Shown in FIGURE 3 is a blood access device 31 which is designed to be semi-permanently implanted in the body, for example, in one's arm, in order to facili-tate repeated entry into the bloodstream of a patient.
For example, such a device allows repeated withdrawing or injection of blood into the patient over a pro-longed period. One illustrative device of this sort is shown in ~. S. Patent No. 4,015,601 issued to Bokros and Slivenko on April 5, 1977. The preferred way of installing such a blood access device 31 is to provide - : .
111~;4SS
it with short vascular grafts 33 which can be appro~
priately sutured to the circulatory system of the body.
The present invention provides a way for coupling these vascular grafts 33 to rigid tubular portions or con-nectors 35 which form a part of the lower portion of the blood access device 31.
As best seen in FIGURE 4, the vascular grafts 33 are sized to just fit ov~-r the exterior surface of ~the tubular portions 35 of the hlood access device, and preferably a shallow depression or groove 37 is provided adjacent the end of each of the tubular portions. ~
coupling element 3'3 is formed in the shape of a ring, from a nic]~el-titanium alloy, having an inner diameter j-~st sufficiently larger than the ~roove diameteJ to allow fox the wall thickness oE tne end portion of the vascular graft 33 in a totally compressed condition.
When the coupling 39 is cooled to a temperature below its transition-temperature range, it becomes duc-tile, and it is then uniformly expanded to a size just large enough to allow it to slip onto the end of the ,~ vascular graft 33 after it has been installed on the tubular portion 35 of the blood access device. By heat-ing the coupling element 39 back above its transition-temperature range, the expanded metal alloy ring returns ; 25 to its precise original shape-and thus s~ueezes the end of the vascular graft 33 tightly into the shallow groove 37. As a result of the precise tolerances, it is as-sured that the graft 33 cannot separate from the blood access device 31 without physically destroying either the coupling ring 39 or the rigid tubular end 35 of the device.
Depicted in FIGURE 5 is a prosthetic applica-tion which demonstrates how an artificial tendon or lig-ament can be securely connected to a bone. Various materials have been developed for use as artificial B tendons or ligaments, and multi-strand Dacro ~material ,e e~ f~d / r~J~ fq~--k ~ :.
11~5455 that has been coated with vapor-deposited carbon shows particular promise for such applications. An expanded sleeve 41 of nickel-titanium alloy is provided as the coupling element, and one end 43 of a prosthetic tendon 45 is fed through the sleeve 41 and then through a hole that has been drilled through the bone 47 of the patient in an appropriate location. The free end 43 of the tendon is then passed back through the sleeve 41 in the opposite direction, as depicted in FIGURE 6A.
The metal alloy is electrically conductive, and an appropriately insulated tool 49, shown diagram-matically in broken lines in FIGURE 6B, which may generally resemble an electrically insulated pair of pliers, can be used to apply electric power to opposite locations on the sleeve 41. The flow of electric cur-rent resistively raises the temperature of the metal alloy above the transition-temperature range and thus causes the expanded sleeve 41 to return to its original shape where it s~ueezes or clamps the two portions of the artificial tendon 45 together in such a manner as to assure there can be no separation, as depicted in FIGURE 6B. Thus, not only does the precision of the amount of compression which can be applied through the use of such a sleeve assure a very tight, permanent con-nection of theend 43Of the artificial tendon to itself, but also the fact that the metal alloy is electrically conductive allows it to be ~uickly heated by the simple application of electrical current after the connection ; with the bone has been made.
Depicted in FIGURE 7 is an alternative em-bodiment of a valve body 51 which is generally similar to the valve body 13 shown in FIGURES 1 and 2. The body 51 is provided with a peripheral groove 53, the upper and lower edges of which are undercut. The fabric sew-ing ring to be installed similarly includes an outer covering 55 of a woven synthetic polymer fabric which is ofasufficient width so as to envelop a generally soft ' .
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ll~S4SS
ring (not shown) of a semi-rigid polymer. A coupling element 57 is employed in the form of a relatively thin annular band which is sized to be snugly received against the flat wall of the undercut groove 53 with room provided to accommodate the thickness of the fabric 55.
The annular band 57, after cooling below its transition temperature, is expanded a sufficient amount .to clear the exterior periphery of the valve body 51.
The annular band is then deformed or folded into a generally U-shaped cross sectional configuration so that it will fit through the opening provided at the edge of the peripheral groove 53. As the coupling element 57 is heated, it shrinks in a circumferential direction while at the same time it expands (as depicted in an intermediate position in FIG. 7) from a U-shape cross section to a straight cross section, in which form it locks the covering 55 to the valve body 51. Instead of substantially expanding the coupling element 57 it could be formed as a split ring of approximately the propor-tion illustrated in FIG. 7. It could then be snapped or deformed into encircling relationship about the valve body and heated to return it to its flattened cross section. Even though such a ring would be split, as opposed to being continuous, it would have a significant advantage over a snap-ring or the like that relies upon spring action for its holding power and which would be inherently subject to stress corrosion problems.~
Although the invention has been described with respect to certain preferred embodiments, it should be understood that various changes and modifications as would be obvious to one having the ordinary skill in the art may be made without departing from the scope of the invention which is defined solely by the appended claims.
For example, although the specification speaks generally of heating the metal alloy to effect its return to its , -: -, ::
, 4~ii5 original shape, certain alloy compositions can be formedwhich have a transition-temperature range below ambient temperature. In such instances, the metal alloy is ap-propriately cooled, using a cryogen or other such source of refrigeration, to lower it to the temperature where it becomes ductile and deformation may take place.
Then,simply by installing and coupling element while -still cold, it can be allowed to simply warm to ambient temperature, causing it to return to its original shape as it passes through the transition-temperature range.
Likewise, the temperature of end use of the product need not be above the transition temperature although the ad-ditional rigidity exhibited at such a temperature is an additional advantage. Various of the features of the invention are set forth in the claims that follow , .
, .BACKGROUND OF THE INVENTION
This invention relates to prosthetic aevices and more particularly to prosthetic devices designed for long-term implantation in the human body wherein it is necessary to make a connection between two components or between~a prosthetic element and an element o~ the human body.
In fabricating prosthetic devices for implanta~
tion in the human body, it often becomes necessary to attach dissimilar materials to each other. One example is the attachment of a fabric sewing cuff to the ex-terior of a housing portion of a heart valve. Hereto-fore, such fabric sewing cuffs have been attached using a circumferential fabric wrapping, a heat-shrinkable synthetic polymer, or a wrapping of metallic wire. How-ever, because it is now hoped that heart valves andother such prosthetic devices, once implanted within the ~! human body, can stay there for the life of the patient, it is important that the joinder remain excellent over a long period of time. It is also desired to eliminate any possibility of failure as a result of mishandling in any ` way, as for example by overheating a heat-shrinkable ` polymer. Moreover, synthetic polymers are inherently -~ subject to creep over their lifetime, and if, for exam-ple, a heart valve should ever break loose from the sew-x- 25 mg cuff, the possible harm to the patient would be most serious.
.'`'` ' ',~' ` , ' . . ` ` . ` I; ' i ` " ' ' '` ' ' `' : .
---` lllS4SS
- la -SUMMARY OF THE INVENTION
In a particular aspect, the invention provides a prosthetic heart valve for long term implantation in the human body including a generally tubular rigid por-tion, a circumscribing sewing ring disposed in encircling relationship to said rigid tubular portion, and a coupling element embedded within said sewing ring for joining said sewing ring to said heart valve tubular portion wherein the improvement comprises said coupling element being made of a nickel-titanium alloy having a transition-temperature range, said element having been formed to a precise shape at a temperature above said range and having been deformed to a different shape at a temperature below said range whereby joinder of said sewing ring to said rigid tubular portion is effected by raising the temperature of said element above said range in order to cause said alloy to attempt to return to said precise shape.
'!
';' , ~, ~,'~'' , `~,`
.. ' '~ .
:..
, ~ .
.''~ .
.,.' ~ , ~.
``"
:: . ,' ,~ - ,,- . . :, ' , ..
`` ~115455 Accordingly, the present invention proyides a method for securely joining a prosthetic element to a natural element of the human bo~y or to another component of the prosthetic device itself. me invention utilizes a coupling element made from a metal alloy which has the novel property of, upon heating, returning to a precise shape from which it has been deformed at a lower temperature. Nickeltitanium alloys have been developed from appro-xImately equiatomic a~ounts of nickel and titanium, and these alloys have a transition-temperature range above which they exhibit an inherent shape memory.
Thus, by machining such an alloy to a precise shape desired for a particular prosthetic application, cooling the alloy below the transition-temperature range and deformlng the cooled alloy by expansion, contraction or bending, it will return to the precise original shape upon warming above the transition temperature. m e precision which such a metal alloy exhibits can be used to t important advantage in prosthetic applications.
BRIEF DESCRIPTION'OF'THE'DRAWINGS
~dvantages of the invention will be apparent from the following de-tailed description when read in conjunction with the appended drawings wherein:
FIGUR~ 1 is a perspective view of a heart valve having a sewing cuff attachel thereto in a manner embodying variGus features of the present in-vention;
i~ .
FIGURE 2 is a sectional view taken generally along line 2-2 of FIGURE 1 with the valve menber shown in the closed position;
FIGURE 3 is a perspective view of a blood access device where arti-~'~ ficial grafts are attached to the entry and exit ends thereof by coupling ele-- ments in accordance with the present invention.
i FIGURE 4 is a sectional view taken along line 4-4 of FIGURE 3;
- FIGURE 5 de nstrates the connection of an artificial tendon or liga-ment to a bone which is a part `
. : : :: .~ ::: :: : . , ; ::- . : , ~, -- :~: , . . :
. .
of a living body;
FIGURES 6A and 6B are enlarged fragmentary views illustrating the connection shown in FIGURE 5;
and FIGURE 7 is a fragmentary sectional view general-ly similar to FIGURE 2 showing another method of attach-ment`embodying various features of the present invention.
DESCRIPTION OF THE PREFERRED EMBODIMENTS
Illustrated in FIGURE 1 is a pivoting disc heart valve 11 designed for replacement of a defective valve in a human heart. The heart valve 11 includes a rigid housing or body portion 13 of g enerally tubular shape which has an essentially circular periphery. The housing 13 has a groove 15 formed in the exterior of its side wall. A sewing ring or cuff 17 is attached to the exterior, grooved portion of the side wall and permits the replacement valve 11 to be sutured in place.
The invention is equally applicable to heart valves of various different designs, for example a ball and cage type valve, although a pivoting disc valve is il-lustrated. A circular disc 19 serves as a valve member and pivots or rotates from an open position to a closed position and back to the open position in response to dif-ferential blood pressure. The disc 19 is retained on a shaft 21 which passes through apertures in a pair of support lugs 23. Thus, the disc is free to turn about - the shaft 21 as a pivot point:which is located as an off-center or eccentric axis with respect to the circular disc 19. The interior portion of the housing 13 is ap-39 propriately ta~ered so as to cooperate with the disc 19 in sealing the valve opening. The construction and opera-tion of the valve 11 is more particularly pointed out in U.S. Patent No. 3,546,711,issued December 15, 1970.
The fabric sewing ring 17 has an outer covering 25 of a suitable synthetic polymer fabric, prèferably a polyester, such as that sold under the trademark Dacron, ' . , - :, :
, ~1~5455 which is biocompatible. As seen in FIGURE 2, the sewing ring 17 has embedded therein a coupling element 27 made of a nickel-titanium alloy, and dis-posed exterior thereof there is provided a larger, generally soft ring 29 of a suitable synthetic plastic material, such as a fluorosilicone rubber or some similar semi-rigid polymer that is biocompatible and capable of sterilization.
` The coupling element 27 is made of a nickel-tita~ium alloy of the type marketed under the trademarkNitinol by RayChem, Co. These metal alloys, contain-ing about 50 percent atoms of nickel and about 50 percent atoms of titanium, have a transition-tempera-ture range above which the alloy will return to a precise fabricated shape. Accordingly, the coupling ele-ment 27 is formed to the precise shape desired by molding, casting, machining or the like at a tempera-ture above the transition-temperature. The particular transition-temperature range is dependent upon the precise metallic composition of the alloyr and it can be varied in order to tailor the alloy to a particu-lar application. Such a change in transition-tempera-ture range is accomplished in either of two ways: by adding additional nickel in excess of the 50:50 ratio ;~ 25 or by substituting a particular atomic amount of cobalt for the same atomic amount of nickel. For a pros-thetic device, an alloy is preferably used which be-comes ductile at a temperature below normal body tem-- perature, i.e., at about 37C. or below although al-loys having a higher transition temperature may be `~ employed.
Below the transition-temperature range, these metallic alloys exhibit excellent ductility and may be deformed in an amount of up to 8 percent without inhibiting their ability to return to the precise origi-nal configuration. The strain which is introduced by ,. _ ~llS455 physical deformation at a temperature below the transition-temperature ran~e, is, in effect, a stora~e of energy, and when the alloy is heated to and through the temperature-transition range, the alloy quickly tries to return to its original shape. Consequently, the coupling element 27 becomes physically entrapped within the groove 15 in the sidewall of the housing from which it cannot escape. By forming the coupling element 27 to precise dimensionsl and similarly holding a close toler-ance on the exterior demension of the heart valve housing13, ti~e fabric covering 25 for the sewing ring is securely squeezed between the coupling element and the rigid grooved wall, and the sizilig may be such that the ring 27 cannotquite return and thus it will remain with a predetermined amount of tensile stress throughout. The alloy is rigid and unyielding above the transition-temperature range, and advantage can further be taken of this property to create a secure joinder.
After assembly of the coupling element-27and the fabric covering 25, the semi-rigid ring 29 is installed, and the fabric covering is then enveloped about it and sewn together at a suitable circular seam using standard techniques. This metallurgically homogeneous coupling element 27 joins the sewin~ ring 17 to the valve body 13 in so secure a manner that there is no reasonable chance of the ring 17 parting from the housin~ 13 even after years of implantation in the body of the patient.
Shown in FIGURE 3 is a blood access device 31 which is designed to be semi-permanently implanted in the body, for example, in one's arm, in order to facili-tate repeated entry into the bloodstream of a patient.
For example, such a device allows repeated withdrawing or injection of blood into the patient over a pro-longed period. One illustrative device of this sort is shown in ~. S. Patent No. 4,015,601 issued to Bokros and Slivenko on April 5, 1977. The preferred way of installing such a blood access device 31 is to provide - : .
111~;4SS
it with short vascular grafts 33 which can be appro~
priately sutured to the circulatory system of the body.
The present invention provides a way for coupling these vascular grafts 33 to rigid tubular portions or con-nectors 35 which form a part of the lower portion of the blood access device 31.
As best seen in FIGURE 4, the vascular grafts 33 are sized to just fit ov~-r the exterior surface of ~the tubular portions 35 of the hlood access device, and preferably a shallow depression or groove 37 is provided adjacent the end of each of the tubular portions. ~
coupling element 3'3 is formed in the shape of a ring, from a nic]~el-titanium alloy, having an inner diameter j-~st sufficiently larger than the ~roove diameteJ to allow fox the wall thickness oE tne end portion of the vascular graft 33 in a totally compressed condition.
When the coupling 39 is cooled to a temperature below its transition-temperature range, it becomes duc-tile, and it is then uniformly expanded to a size just large enough to allow it to slip onto the end of the ,~ vascular graft 33 after it has been installed on the tubular portion 35 of the blood access device. By heat-ing the coupling element 39 back above its transition-temperature range, the expanded metal alloy ring returns ; 25 to its precise original shape-and thus s~ueezes the end of the vascular graft 33 tightly into the shallow groove 37. As a result of the precise tolerances, it is as-sured that the graft 33 cannot separate from the blood access device 31 without physically destroying either the coupling ring 39 or the rigid tubular end 35 of the device.
Depicted in FIGURE 5 is a prosthetic applica-tion which demonstrates how an artificial tendon or lig-ament can be securely connected to a bone. Various materials have been developed for use as artificial B tendons or ligaments, and multi-strand Dacro ~material ,e e~ f~d / r~J~ fq~--k ~ :.
11~5455 that has been coated with vapor-deposited carbon shows particular promise for such applications. An expanded sleeve 41 of nickel-titanium alloy is provided as the coupling element, and one end 43 of a prosthetic tendon 45 is fed through the sleeve 41 and then through a hole that has been drilled through the bone 47 of the patient in an appropriate location. The free end 43 of the tendon is then passed back through the sleeve 41 in the opposite direction, as depicted in FIGURE 6A.
The metal alloy is electrically conductive, and an appropriately insulated tool 49, shown diagram-matically in broken lines in FIGURE 6B, which may generally resemble an electrically insulated pair of pliers, can be used to apply electric power to opposite locations on the sleeve 41. The flow of electric cur-rent resistively raises the temperature of the metal alloy above the transition-temperature range and thus causes the expanded sleeve 41 to return to its original shape where it s~ueezes or clamps the two portions of the artificial tendon 45 together in such a manner as to assure there can be no separation, as depicted in FIGURE 6B. Thus, not only does the precision of the amount of compression which can be applied through the use of such a sleeve assure a very tight, permanent con-nection of theend 43Of the artificial tendon to itself, but also the fact that the metal alloy is electrically conductive allows it to be ~uickly heated by the simple application of electrical current after the connection ; with the bone has been made.
Depicted in FIGURE 7 is an alternative em-bodiment of a valve body 51 which is generally similar to the valve body 13 shown in FIGURES 1 and 2. The body 51 is provided with a peripheral groove 53, the upper and lower edges of which are undercut. The fabric sew-ing ring to be installed similarly includes an outer covering 55 of a woven synthetic polymer fabric which is ofasufficient width so as to envelop a generally soft ' .
~, ~
ll~S4SS
ring (not shown) of a semi-rigid polymer. A coupling element 57 is employed in the form of a relatively thin annular band which is sized to be snugly received against the flat wall of the undercut groove 53 with room provided to accommodate the thickness of the fabric 55.
The annular band 57, after cooling below its transition temperature, is expanded a sufficient amount .to clear the exterior periphery of the valve body 51.
The annular band is then deformed or folded into a generally U-shaped cross sectional configuration so that it will fit through the opening provided at the edge of the peripheral groove 53. As the coupling element 57 is heated, it shrinks in a circumferential direction while at the same time it expands (as depicted in an intermediate position in FIG. 7) from a U-shape cross section to a straight cross section, in which form it locks the covering 55 to the valve body 51. Instead of substantially expanding the coupling element 57 it could be formed as a split ring of approximately the propor-tion illustrated in FIG. 7. It could then be snapped or deformed into encircling relationship about the valve body and heated to return it to its flattened cross section. Even though such a ring would be split, as opposed to being continuous, it would have a significant advantage over a snap-ring or the like that relies upon spring action for its holding power and which would be inherently subject to stress corrosion problems.~
Although the invention has been described with respect to certain preferred embodiments, it should be understood that various changes and modifications as would be obvious to one having the ordinary skill in the art may be made without departing from the scope of the invention which is defined solely by the appended claims.
For example, although the specification speaks generally of heating the metal alloy to effect its return to its , -: -, ::
, 4~ii5 original shape, certain alloy compositions can be formedwhich have a transition-temperature range below ambient temperature. In such instances, the metal alloy is ap-propriately cooled, using a cryogen or other such source of refrigeration, to lower it to the temperature where it becomes ductile and deformation may take place.
Then,simply by installing and coupling element while -still cold, it can be allowed to simply warm to ambient temperature, causing it to return to its original shape as it passes through the transition-temperature range.
Likewise, the temperature of end use of the product need not be above the transition temperature although the ad-ditional rigidity exhibited at such a temperature is an additional advantage. Various of the features of the invention are set forth in the claims that follow , .
Claims (4)
1. A prosthetic heart valve for long term implanta-tion in the human body including a generally tubular rigid portion, a circumscribing sewing ring disposed in encircling relationship to said rigid tubular portion, and a coupling element embedded within said sewing ring for joining said sewing ring to said heart valve tubular portion wherein the Improvement comprises said coupling element being made of a nickel-titanium alloy having a transition-temperature range, said element having been formed to a precise shape at a tempera-ture above said range and having been deformed to a different shape at a temperature below said range whereby joinder of said sewing ring to said rigid tubular portion is effected by raising the temperature of said element above said range in order to cause said alloy to attempt to return to said precise shape.
2. A device in accordance with Claim 1 wherein said coupling element is a continuous ring.
3. A device in accordance with Claim 1 wherein said coupling element is a split ring of generally U-shaped cross section.
4. A device in accordance with any one of Claims 1, 2 and 3 wherein the transition-temperature at which said metal alloy becomes ductile is about 20°C. or below.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US907,664 | 1978-05-19 | ||
| US05/907,664 US4233690A (en) | 1978-05-19 | 1978-05-19 | Prosthetic device couplings |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1115455A true CA1115455A (en) | 1982-01-05 |
Family
ID=25424440
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA327,878A Expired CA1115455A (en) | 1978-05-19 | 1979-05-18 | Inherent shape memory coupling for heart valve |
Country Status (6)
| Country | Link |
|---|---|
| US (1) | US4233690A (en) |
| JP (1) | JPS54155696A (en) |
| CA (1) | CA1115455A (en) |
| DE (1) | DE2920191A1 (en) |
| FR (1) | FR2425846A1 (en) |
| GB (1) | GB2021420A (en) |
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Family Cites Families (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US3859668A (en) * | 1972-08-11 | 1975-01-14 | Medical Inc | Rotatable suturing member |
| US3786806A (en) * | 1972-11-22 | 1974-01-22 | A Johnson | Thermoconstrictive surgical appliance |
| DE2703529A1 (en) * | 1977-01-28 | 1978-08-03 | Krupp Gmbh | IMPLANT TO CONNECT SEPARATION SITES IN LIVING TISSUE |
-
1978
- 1978-05-19 US US05/907,664 patent/US4233690A/en not_active Expired - Lifetime
-
1979
- 1979-05-18 JP JP6141279A patent/JPS54155696A/en active Pending
- 1979-05-18 CA CA327,878A patent/CA1115455A/en not_active Expired
- 1979-05-18 GB GB7917457A patent/GB2021420A/en not_active Withdrawn
- 1979-05-18 FR FR7912670A patent/FR2425846A1/en active Granted
- 1979-05-18 DE DE19792920191 patent/DE2920191A1/en not_active Withdrawn
Also Published As
| Publication number | Publication date |
|---|---|
| JPS54155696A (en) | 1979-12-07 |
| US4233690A (en) | 1980-11-18 |
| GB2021420A (en) | 1979-12-05 |
| FR2425846A1 (en) | 1979-12-14 |
| FR2425846B3 (en) | 1982-03-26 |
| DE2920191A1 (en) | 1979-11-22 |
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