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WO2006063108A1 - Diagnostic kit to assist with heart valve annulus adjustment - Google Patents

Diagnostic kit to assist with heart valve annulus adjustment

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Publication number
WO2006063108A1
WO2006063108A1 PCT/US2005/044373 US2005044373W WO2006063108A1 WO 2006063108 A1 WO2006063108 A1 WO 2006063108A1 US 2005044373 W US2005044373 W US 2005044373W WO 2006063108 A1 WO2006063108 A1 WO 2006063108A1
Authority
WO
Grant status
Application
Patent type
Prior art keywords
distal
tube
anchor
proximal
coronary
Prior art date
Application number
PCT/US2005/044373
Other languages
French (fr)
Inventor
Stanton J. Rowe
Henry Bourang
Sepehr Fariabi
Jan Otto Solem
Original Assignee
Edwards Lifesciences Corporation
Priority date (The priority date 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 date listed.)
Filing date
Publication date

Links

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS 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
    • A61F2/00Filters 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
    • A61F2/02Prostheses implantable into the body
    • A61F2/24Heart 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
    • A61F2/2442Annuloplasty rings or inserts for correcting the valve shape; Implants for improving the function of a native heart valve
    • A61F2/2451Inserts in the coronary sinus for correcting the valve shape
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B1/00Instruments for performing medical examinations of the interior of cavities or tubes of the body by visual or photographical inspection, e.g. endoscopes; Illuminating arrangements therefor
    • A61B1/00064Constructional details of the endoscope body
    • A61B1/00071Insertion part of the endoscope body
    • A61B1/0008Insertion part of the endoscope body characterised by distal tip features
    • A61B1/00082Balloons
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Detecting, measuring or recording for diagnostic purposes; Identification of persons
    • A61B5/06Devices, other than using radiation, for detecting or locating foreign bodies ; determining position of probes within or on the body of the patient
    • A61B5/061Determining position of a probe within the body employing means separate from the probe, e.g. sensing internal probe position employing impedance electrodes on the surface of the body
    • A61B5/064Determining position of a probe within the body employing means separate from the probe, e.g. sensing internal probe position employing impedance electrodes on the surface of the body using markers
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/06Measuring blood flow
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/12Diagnosis using ultrasonic, sonic or infrasonic waves in body cavities or body tracts, e.g. by using catheters

Abstract

A diagnostic device for determining the amount of change required in a coronary sinus to reduce valve regurgitation. The device includes a distal tube (14) having a distal anchor (18) at a distal end portion of the distal tube, a proximal tube (12) having a proximal anchor (16) at a distal end portion of the proximal tube, and an adjustor to move the distal tube relative to the proximal tube. The proximal tube and the distal tube together form a telescoping elongate body adapted to fit within the coronary sinus, and the device includes a scale (27) to measure the movement of the distal anchor relative to the proximal anchor.

Description

DIAGNOSTIC KIT TO ASSIST WITH HEART VALVE ANNULUS ADJUSTMENT

This invention relates to apparatus and methods for heart valve repair and, more particularly, to a diagnostic kit to assist with heart valve annulus adjustment for improving heart valve function using devices inserted into vessels surrounding the target valve.

BACKGROUND

Heart valve regurgitation, or leakage from the outflow to the inflow side of a heart valve, is a common occurrence in patients with heart failure and a source of morbidity and mortality in these patients. Usually regurgitation will occur in the mitral valve, located between the left atrium and left ventricle, or in the tricuspid valve, located between the right atrium and right ventricle. Mitral regurgitation in patients with heart failure is caused by changes in the geometric configurations of the left ventricle, papillary muscles and mitral annulus. Similarly, tricuspid regurgitation is caused by changes in the geometric configurations of the right ventricle, papillary muscles and tricuspid annulus. These geometric alterations result in mitral and tricuspid leaflet tethering and incomplete coaptation in systole.

Heart valve repair is the procedure of choice to correct heart regurgitation of all etiologies. With the use of current surgical techniques, between 40% and 60% of regurgitant heart valves can be repaired, depending on the surgeon's experience and the anatomic conditions. The advantages of heart valve repair over heart valve replacement are well documented. These advantages include better preservation of cardiac function and reduced risk of anticoagulant-related hemorrhage, thromboembolism and endocarditis. Recently, several developments in minimally invasive techniques for repairing heart valves without surgery have been introduced. Some of these techniques involve introducing systems for remodeling the mitral annulus through the coronary sinus.

The coronary sinus is a blood vessel commencing at the coronary ostium in the right atrium and passing through the atrioventricular groove in close proximity to the posterior, lateral and medial aspects of the mitral annulus. Because of its position adjacent to the mitral annulus, the coronary sinus provides an ideal conduit for positioning an endovascular prosthesis to act on the mitral annulus and thereby reshape it.

Examples of minimally invasive apparatus for heart valve repair can be found in U.S. Patent No. 6,210,432 to Solem, et al., U.S. Ser. No. 09/775,677 to Solem, et. al. filed on February 5, 2001, U.S. Ser. No. 10/303,765 to Solem, et. al. filed on November 26, 2002, U.S. Ser. No. 10/141,348 to Solem, et. al. filed on May 9, 2002, U.S. Ser. No. 10/329,720 to Solem, et. al. filed on December 24, 2002, U.S. Ser. No. 10/714,462 to Solem, et. al. filed on November 13, 2003 and U.S. Ser. No. 60/530352 to Solem, et al. filed on December 16, 2003 (the '352 application) all of which are incorporated herein by reference.

One specific example of a minimally invasive apparatus for heart valve repair, as described in greater detail in the '352 application, and as shown in FIGs. 10 and 11 herein, includes an elongate body 410 having a proximal anchor 412 and a distal anchor 414 connected by a bridge 416. The proximal and distal anchors 412, 414 are both stents made from nitinol and both anchors have a mesh configuration including loops 54 of zigzag shaped material having alternating peaks 42. The loops 54 are connected at each peak 42 to form rings 56 of four- sided openings. Both the proximal anchor 412 and the distal anchor 414 are transferable between a compressed state, in which the anchors have a diameter that is less than the diameter of the coronary sinus, and an expanded state, in which the anchors have a diameter that is about equal to or greater than the diameter of the coronary sinus.

As shown in FIG. 10, the bridge 416 is connected between the proximal anchor 412 and the distal anchor 414 by links 418, 419. As shown in more detail in FIG. 11, the link 419 has a base 421 and arms 422 that extend from the base and which are connected to the anchor 414. The link also includes a hole 428 which serves as a means through which resorbable thread 420 may be secured to the bridge.

The bridge 416 is made from a shape memory material and is flexible to allow the body 410 to conform to the shape of the coronary sinus. The bridge 416 includes connected X-shaped elements 424 having a space 425 between adjacent elements. The bridge has two states, an activated state in which the bridge 416 has a first length and a non-activated state, in which the bridge has a second length, the second length being longer than the first length. Resorbable thread 420 which acts as a temporary spacer is woven into the spaces 425 to hold the bridge in its longer non-activated state.

The body is inserted into the coronary sinus of a patient with both anchors 412, 414, in the compressed state and the bridge 416 including resorbable thread 420 in the longer non-activated state. After the anchors 412, 414 are placed in a desired location, they are transformed into their expanded state in which they serve to attach the body 410 to the coronary sinus. After a period of time, during which the wall of the coronary sinus grows around the anchors 412, 414, the resorbable thread dissolves and the bridge 416 transforms from its longer non-activated state to its shorter activated state. The shortening of the bridge 416 draws the proximal anchor 412 and the distal anchor 414 closer together, cinching the coronary sinus and reducing its circumference. This reduction of the circumference of the coronary sinus closes the gap causing mitral regurgitation.

Valve annulus reshaping devices, including those described above, may be manufactured such that they can vary in certain dimensions or characteristics. For instance, the devices may be manufactured so that they foreshorten or otherwise change shape by a specific amount depending on how much reshaping of a valve is necessary. In other words, a physician may have a choice between using a reshaping device that severely remodels an annulus, one that only slightly remodels an annulus, or one that is custom designed to remodel an annulus by a specific amount. Additionally, the valve reshaping devices may also be manufactured to have different lengths and/or anchor sizes. Due to varying degrees of the severity of mitral and tricuspid valve leaflet coaptation as well as varying sizes and lengths of heart valve annuli, it would be advantageous for a physician to know how much reshaping of the valve annulus is necessary as well as having an idea of the size and length of the annulus before inserting the valve reshaping device. This knowledge would allow the physician to choose a device that could reshape the valve annulus by an appropriate amount. Thus, there is a need for a device that a physician may use to gauge the amount of reshaping necessary in a heart valve annulus and/or the size and length of the annulus. Such a device would allow the physician to select an annulus reshaping device to insert into a patient that more closely approximates the amount of reshaping necessary for that specific patient as well as a device that may be custom designed to fit the size and length of the patient's annulus. SUMMARY

A diagnostic device for determining the amount of change desired in a cardiac vessel to reduce valve regurgitation is disclosed. The diagnostic device comprises a distal tube (or other suitable elongate body) having a distal anchor attached at a distal end of the distal tube, a proximal tube (or other suitable elongate body) having a proximal anchor attached at a distal end of the proximal tube, and an adjustor by which the distal tube may be moved relative to the proximal tube. In one embodiment, the device may be inserted into the coronary sinus. The proximal tube and the distal tube together form a telescoping elongate body adapted to fit within the coronary sinus.

Additionally, the distal tube includes a plurality of radiopaque markers spaced evenly thereon to provide a means for measuring the distance moved by the distal tube relative to the proximal tube, the distal anchor and the proximal anchor are transformable between a compressed state and an expanded state, and movement of the adjustor by a specified distance causes movement of the distal tube by the same distance. The proximal and distal anchors may be balloons, baskets or stents.

A method for determining the amount of change to the coronary sinus necessary to reduce mitral regurgitation is also disclosed. Such method includes inserting a diagnostic device into the coronary sinus, anchoring a distal anchor to the coronary sinus, anchoring a proximal anchor to the coronary sinus, using an adjustor to move the distal anchor proximally such that mitral regurgitation is reduced and measuring the proximal movement of the distal anchor and simultaneously measuring the amount of mitral valve regurgitation.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a three-dimensional view of the mitral valve and coronary sinus. FIG. 2 is a side view of one exemplary embodiment of a diagnostic device of the present invention including a proximal tube with a proximal anchor and a distal tube with a distal anchor in a compressed state.

FIG. 3 is a side view of embodiment of FIG. 2 including a proximal anchor and a distal anchor in an expanded state.

FIG. 4a is a cross-sectional view of a telescoped proximal tube and distal tube of the current invention.

FIG. 4b is a cross-sectional view of a distal tube of the current invention.

FIG. 5 is a cross-sectional view of a coaxial proximal tube and distal tube of the current invention.

FIG. 6 is a perspective view of an alternate anchor according to the present invention.

FIG. 7 is a side view of the diagnostic device of FIG. 2 after the device has been initially inserted into the coronary sinus and before expansion of the distal anchor.

FIG. 8 is a side view of the diagnostic device of FIG. 2 positioned for use in the coronary sinus with the distal anchor and the proximal anchor in the expanded state.

FIG. 9 is a side view of the diagnostic device of FIG. 2 after the device has been used to reduce an anterior-posterior distance between leaflets of a mitral valve.

FIG. 10 is an exemplary embodiment of a recent mitral valve repair device.

FIG. 11 is a detail of the mitral valve repair device of FIG. 10. DETAILED DESCRIPTION

Although the devices and methods described below may be used in any appropriate heart valve annulus, for ease and consistency of explanation the devices and methods below will be described with specific reference to the mitral valve and mitral annulus.

Referring to FIG. 1, a coronary sinus 20 extends from a right atrium 22 and a coronary ostium 24 and wraps around a mitral valve 26. The term coronary sinus is used herein as a generic term to describe a portion of the vena return system that is situated adjacent to the mitral valve 26 along the atrioventricular groove. The term coronary sinus 20 used herein generally includes the coronary sinus, the great cardiac vein and the anterior interventricular vein. A mitral annulus 28 is a portion of tissue surrounding a mitral valve orifice to which several leaflets attach. The mitral valve 26 has two leaflets, an anterior leaflet 29 and a posterior leaflet 31. The posterior leaflet has three scallops Pl, P2 and P3 which, in a healthy mitral valve coapt with the anterior leaflet 29 to prevent regurgitation of blood through the valve.

The problem of mitral regurgitation often results when a posterior aspect of the mitral annulus 28 dilates and displaces one or more of the posterior leaflet scallops Pl, P2 or P3 away from the anterior leaflet 29 causing a gap to be formed through which regurgitation occurs. To reduce or eliminate mitral regurgitation, therefore, it is desirable to move the posterior aspect of the mitral annulus 28 in an anterior direction and close the gap caused by the leaflet displacement.

As shown in FIGs. 2 and 3, an embodiment of the diagnostic device 10 of the present invention comprises a proximal tube 12 and a distal tube 14. The diagnostic device 10 may be of dimensions such that it is insertable into a vessel adjacent a heart valve such as the coronary sinus and the anterior right ventricular cardiac vein. Additionally, the diagnostic device 10 may be flexible enough to allow it to adapt to the curvature of the vessel into which it is inserted.

As shown in FIG. 4a, the proximal tube 12 may be a plastic tube having two lumens, a tube lumen 35 and an inflation lumen 37. The tube lumen 35 allows the distal tube 14 to pass through the proximal tube 12. The inflation lumen serves as a channel through or by which an inflation gas or liquid may expand an anchor, as is also described in greater detail below. This tube configuration may be used when the anchor is inflatable, such as a balloon. In one preferred construction, the proximal tube is formed of nylon tubing having an outer diameter of about 0.130 inches. The tube lumen 35 preferably has a diameter of about 0.085 inches. In one alternative embodiment, the inflation lumen in the proximal tube may be formed with a crescent or oval shape. In another alternative embodiment, the proximal tube may be formed with two or more inflation lumens to increase the cross-sectional flow area. In yet another alternative embodiment, the proximal portion of the proximal tube may be fitted with a plastic strain relief tubing and a hub for communicating with the tube lumen and inflation lumen.

As shown in FIG. 4b, the distal tube may also contain two lumens, a guidewire lumen 19 and an inflation lumen 21. The guidewire lumen 19 serves as a channel on which the distal tube 14 may travel as it is inserted into a patient as is described in greater detail below. In one preferred embodiment, the guidewire lumen 19 is formed with a diameter of about 0.042 inches. The inflation lumen 21 serves as a channel through or by which an inflation gas or liquid may expand an anchor, as is also described in greater detail below. This tube configuration may be used when the anchor is inflatable, such as a balloon. In one preferred construction, the distal tube is formed of Pebax 55D tubing having an outer diameter of about 0.067 inches. The guidewire lumen 19 preferably has a diameter of about 0.042 inches. In one alternative embodiment, the inflation lumen in the distal tube may be formed with a crescent or oval shape. In another alternative embodiment, the distal tube may be formed with two or more inflation lumens to increase the cross-sectional flow area through the tube. In yet another alternative embodiment, the proximal portion of the distal tube is surrounded by a stainless steel braided polyamide tubing having an inner diameter of about 0.0725 inches and an outer diameter of about 0.0780 inches to stiffen the proximal portion and enhance pushability. The proximal portion may also be fitted with a hub for communication with the guidewire and inflation lumens.

FIG. 5 shows an alternate configuration wherein the distal tube 14 includes an inner tube 68 and an outer tube 66 that are coaxial. Based on this configuration, a guidewire lumen 64 is formed inside the inner tube 68 and an expansion lumen 62 is formed between the inner tube and the outer tube 66. This tube configuration may be used when the anchor is inflatable, such as a balloon, or mechanically expandable, such as a basket. This coaxial tube configuration may also be used for the proximal tube 12. It will also be appreciated that in some configurations the proximal tube 12 passes through the distal tube, rather than vice versa, as described above.

The distal tube 14 may further include radiopaque marker bands 27 spaced along the outer perimeter of the tube as shown in FIG. 2. The marker bands 27, which are visible under fluoroscopy, serve to indicate the position of the distal tube 14 when the tube is positioned within a vessel. Additionally, the marker bands 27 may be used to measure a desired portion of the coronary sinus and the amount of movement by the distal tube 14 as is described in greater detail below. The marker bands 27 may be platinum bands or any other biocompatible band visible under fluoroscopy or other suitable visual means. The specific number of bands 27 included along the distal tube 14 is not critical, but preferably there are a sufficient number of bands to allow the entire exposed length of the tube in the coronary sinus to be visible under fluoroscopy. In one preferred embodiment, the distal tube comprises marker bands disposed along about 14 cm of the distal end portion. The marker bands are preferably spaced apart by about 1 cm. Further, there are a sufficient number of bands 27 to allow the bands to act as distance markers for movement of the distal tube 14. A similar number of markers are located on the distal tube outside of the patient visible for the human eye. These markers are visible and may be counted even without the help of fluoroscopy.

The distal tube 14 also includes a distal anchor 18 located at or near the distal end of the distal tube. In one embodiment, the distal anchor 18 has two states, a compressed state and an expanded state. In the compressed state, the distal anchor 18 is insertable into the coronary sinus 20 or other coronary vessel. In the expanded state, the distal anchor 18 secures the distal tube 14 to an inner wall of the vessel into which it has been inserted. The distal anchor 18 is transformable from the compressed state to the expanded state by a transformation means. Such transformation means may be mechanical, electrical or chemical. Additionally, the distal anchor 18 may be self- expanding.

As shown in FIGs. 2 and 3 in one exemplary embodiment, the distal anchor 18 is a compliant balloon which conforms to the size and shape of the vessel into which it is expanded. The balloon may be attached to the distal or proximal tube by a thermal or adhesion bond, or by any other appropriate attachment means. The balloon may be manufactured such that it has a safety mechanism that will reduce the possibility of the balloon damaging a vessel into which it is inserted. For instance, the balloon may be designed to have a maximum pressure to which it can be inflated. Additionally, the balloon may be designed with a "slow leak" which gradually reduces its internal pressure. Since the compliant balloon will conform to the size of the vessel and because the balloon is visible under fluoroscopy, an observer will be able determine the size of the vessel at the balloon location by viewing the balloon on a screen having dimension markers. Knowing the approximate size of the vessel into which a valve repair device will be inserted may allow for a more accurate decision to be made as to which particular valve repair device should be selected from an array of devices to use on a patient. In one preferred configuration, the distal anchor 18 is a compliant balloon formed of Pebax 55D and having a length of about 20 mm. The compliant balloon preferably has inflated diameters ranging from about 4 mm at 1 atmosphere to about 9 mm at 8 atmospheres. In alternative configurations, the balloon may be formed of any other suitable material, such as, for example, nylon, polyurethane and polyethylene. In one embodiment, the distal tubing is further provided with an atraumatic distal tip. The distal tip is preferably made of Pebax 4OD. In other alternate embodiments of the diagnostic device 10, the distal anchor 18 may be a basket, a stent, or any other expandable device adapted to secure the device inside a vessel.

The balloon may be transformed from its compressed state to its expanded state by using a biocompatible fluid, and more specifically, a saline solution. The fluid may be introduced through a catheter (not shown) and may be transported through the inflation lumen 21, 62 (FIGs. 4 and 5) to the balloon.

In an alternate embodiment as shown in FIG. 6, a basket 30 may be used as a distal anchor. In one embodiment, the basket 30 has two states, a compressed state and an expanded state. In the compressed state, the basket 30 is insertable into the coronary sinus or other coronary vessel. More specifically, in the compressed state the basket 30 may be substantially cylindrical and may include a plurality of strands 32 extending longitudinally from a proximal end 34 to a distal end 36 of the basket spaced evenly around the basket's circumference. The distal end 36 of the basket 30 may be adapted to be fitted onto an inner tube 68 and the proximal end 34 of the basket may be adapted to be fitted onto an outer tube 66 (see FIG. 5). In one embodiment, the outer tube 66 may also be the distal tube 14. When the inner tube 68 and the outer tube 66 are moved relative to each other, the basket 30 may be expanded or contracted. In the expanded state, the basket 30 is secured to an inner wall of the vessel into which it has been inserted. In the expanded state, wherein the distance between the proximal end 34 and the distal end 36 of the basket 30 is decreased, the strands 32 may become triangularly-shaped with the apex of the triangle protruding away from the center of the basket. In one exemplary embodiment, the strands 32 may be made from a shape memory material (e.g. nitinol) allowing the basket 30 to transform from its compressed state to its expanded state by, for example, retraction of a sheath (not shown) covering the basket.

Similarly to the distal tube 14, the proximal tube 12 may have a proximal anchor 16 located at or near the distal end of the proximal tube. Like the distal anchor 18, the proximal anchor 16 may have a compressed state for delivery into a vessel and an expanded state for anchoring the distal tube to the vessel. The proximal tube 12 may further include an inflation lumen 37 for transforming the proximal anchor 16 between the compressed state and the expanded state. In one preferred configuration, the proximal anchor 16 is a balloon having a length of about 30 mm and formed of polyurethane. In alternative configurations, the balloon may be formed of any other suitable material, such as, for example, nylon, Pebax and polyethylene. The distal tube 14 and the proximal tube 12 of the diagnostic device 10 may be slidably connected to each other in a telescoping manner to form an elongate body. In one exemplary embodiment, the outer diameter of the proximal tube 12 is greater than the outer diameter of the distal tube 14, allowing the distal tube to fit within the proximal tube. The movement of the distal tube 14 may be controlled by using a handle (not shown). More specifically, the distal tube 14 may be attached to a collar which is slidable along the handle. When the collar is moved proximally, the distal tube 14 is also moved proximally by the same distance. Similarly, when the collar is moved distally, the distal tube 14 is moved distally by the same distance. In one exemplary embodiment, the body of the handle may include distance markers which allow the movement of the collar, and thus the movement of the distal tube 14, to be measured.

In one exemplary embodiment, the diagnostic device 10 may be deployed as follows. First, a guide wire (not shown) is inserted into the coronary sinus past the great cardiac vein and deep into the arterioventricular vein. The diagnostic device 10 may be mounted coaxially on a delivery catheter (not shown), and inserted into the coronary sinus 20 over the guidewire. Proximal ends of the distal tube 14 and proximal tube 12 may extend out of the patient's body where they are attached to a handle. Additionally, the proximal anchor 16 and the distal anchor 18 are adjacent as the diagnostic device 10 is inserted into the coronary sinus 20.

When initially inserted into a patient, the diagnostic device 10 is inserted into the coronary sinus 20 as distally as possible. Specifically, the diagnostic device 10 may be inserted into the part of the coronary sinus known as the great cardiac vein 46 as shown in FIG. 7. Because of its naturally curved shape and higher concentration of fatty tissue, the great cardiac vein 46 allows for high resistance to movement and provides a natural anchoring location for the distal anchor 18.

Once the distal tube 14, and more specifically, the distal anchor 18 have been placed in the desired position in the coronary sinus 20, the distal anchor may be transformed from its compressed state into its expanded state. In one embodiment, where the distal anchor 18 is a balloon, a biocompatible fluid will be introduced into the inflation lumen 37 to inflate the balloon. In an alternate embodiment, where the distal anchor 18 is a mechanically expandable anchor, such as a basket 30 (FIG. 6), manipulation of the inner tube 68 and the outer tube 66 (FIG. 5) will cause the anchor to transform into its expanded state. In yet another embodiment, where the anchor is self-expandable, a delivery sheath is used to cover the anchors and retraction of the delivery sheath will cause the anchor to transform into its expanded state.

Once the distal anchor 18 has been expanded such that the anchor is in contact with the inner walls of the coronary sinus 20, the proximal tube 12 is pulled proximally using the handle. The distance markers on the handle as well as the radiopaque markers 27 on the distal tube 14 allow the distance that the proximal tube 12 has moved to be measured. The proximal tube 12 is pulled proximally until the proximal anchor 16 is adjacent the ostium 24 of the coronary sinus 20. Alternatively, the proximal anchor may be placed in the right atrium outside of the coronary sinus ostium 24, abutting the ostium, but not blocking the ostium. Radiopaque markers 27 on the distal tube 14 are visible on a monitoring screen and aid a user in locating the proximal anchor 16 in the coronary sinus 20. After the proximal anchor 16 is placed in its desired location, the proximal anchor is transformed from its compressed state into its expanded state (FIG. 8). As described above, in an embodiment wherein the proximal anchor 16 is a balloon, a biocompatible fluid will be introduced into the inflation lumen 21 to inflate the balloon In the embodiment wherein the proximal anchor 16 is a self- expanding anchor, such as a basket 30 (FIG. 6), the retraction of the delivery sheath proximal to the proximal anchor will cause the anchor to transform into its expanded state.

Once both the proximal anchor 16 and the distal anchor 18 have been transformed from their compressed state into their expanded state, the handle may be used to pull the distal tube 14 proximally. Pulling the distal tube 14 proximally will have at least one of two effects on the coronary sinus 20. The first effect may be to cinch the coronary sinus 20 tighter around the mitral valve 26, decreasing the distance between the anterior leaflet 29 and posterior leaflets 31. The second effect may be to decrease the radius of curvature of the coronary sinus 20, which may also decrease the distance between the anterior leaflet 29 and posterior leaflets 31. This change in the shape of the mitral valve 26 allows the gap caused by mitral regurgitation between the anterior leaflet 29 and the posterior leaflet 31 to close (FIG. 9), thus decreasing or eliminating mitral regurgitation.

As the radius of curvature of the coronary sinus is decreased and the gap between the anterior leaflet 29 and posterior leaflet 31 of the mitral valve is reduced, the amount of regurgitation is measured. This measurement is preferably performed by ultrasound with the ultrasound probe located on the chest, in the esophagus or inside the heart of the patient. When the regurgitation is at a minimum, and particularly when there is no regurgitation, the distance the distal tube 14 has moved relative to the proximal tube is noted, for instance, by using the radiopaque markers as a measuring tool.

Once mitral regurgitation has been eliminated or reduced by the desired amount, and the distance the distal tube 14 must be moved to achieve the desired effect has been measured, the distal anchor 18 and the proximal anchor 16 are transformed back from their expanded state to their compressed state. In the embodiment where the anchors 16, 18 are balloons, the fluid used to inflate the balloons is removed. In the embodiment where the anchors 16, 18 are self- expanding, the delivery sheath is reinserted over each anchor. In the embodiment where the anchors 16, 18 are baskets 30, the inner tube 68 and the outer tube 66 are moved apart from one another to transform the anchor into its compressed state.

After the proximal anchor 16 and the distal anchor 18 have been returned to their compressed state, the proximal tube 12 and the distal tube 14 are retracted proximally along the guide wire from the coronary sinus 20 and out of the patient's body. Once the diagnostic device 10 has been removed, a valve repair device may be inserted along the guidewire to more permanently repair the mitral valve regurgitation. Based on information about the coronary sinus 20 received from the diagnostic device 10, such as the length of the coronary sinus, and information about the amount of foreshortening necessary to achieve the desired reduction of mitral regurgitation, an appropriate valve repair device may be selected from an array of such devices having various (or variable) diameters and/or foreshortening lengths.

While the foregoing described the preferred embodiments of the invention, it will be obvious to one skilled in the art that various alternatives, modifications and equivalents may be practiced within the scope of the appended claims.

Claims

WHAT IS CLAIMED IS:
1. A diagnostic device for determining an amount of adjustment required in a coronary sinus to reduce heart valve regurgitation comprising:
a first elongate body having a distal anchor at a distal end portion of the first elongate body,
a second elongate body having a proximal anchor at a distal end portion of the second elongate body, and
an adjustor to move one of the first and second elongate body relative to the other of the first and second elongate bodies,
wherein the first and second elongate bodies together form a telescoping elongate body adapted to fit within the coronary sinus, and
further comprising a scale to permit measurement of the movement of the distal anchor relative to the proximal anchor.
2. The diagnostic device of claim 1, wherein the scale is on the elongate body.
3. The diagnostic device of claim 2, wherein the scale is a plurality of markers.
4. The diagnostic device of claim 3, wherein the markers are spaced evenly along the elongate body.
5. The diagnostic device of claim 1, wherein the scale is on the adjustor.
6. The diagnostic device of claim 1, wherein the distal anchor and the proximal anchor are transformable between a compressed state and an expanded state.
7. The diagnostic device of claim 1, wherein movement of the adjustor by a certain distance causes movement of the distal tube by the same distance.
8. The diagnostic device of claim 1, wherein the distal anchor and the proximal anchor are balloons.
9. The diagnostic device of claim 8, wherein the distal anchor and the proximal anchors are transformed from their compressed state to their expanded state by a fluid.
10. The diagnostic device of claim 1, wherein the distal anchor is a basket.
11. The diagnostic device of claim 1 , wherein each of the first and second elongated bodies contain an inflation lumen and a guidewire lumen.
12. The diagnostic device of claim 1, wherein the adjustor is a handle.
13. A method for determining an amount of adjustment to a coronary sinus necessary to reduce heart valve regurgitation comprising:
inserting a diagnostic device into a coronary vessel adjacent to the cardiac valve, the diagnostic device including a distal anchor and a proximal anchor,
anchoring the distal anchor to the coronary sinus,
anchoring the proximal anchor to the coronary sinus,
adjusting at least one of the distal and proximal anchors to reduce heart valve regurgitation, and
measuring the adjustment.
14. The method of claim 13, wherein anchoring the proximal and distal anchors comprises expanding the anchors from a compressed state to an expanded state.
15. The method of claim 13, wherein expanding the distal anchor and the proximal anchor comprises expanding by a fluid.
16. The method of claim 13, wherein inserting the diagnostic device comprises inserting the diagnostic device into a great cardiac vein portion of the coronary sinus.
17. The method of claim 13, wherein adjusting comprises straightening the curvature of the coronary sinus.
18. The method of claim 13 wherein adjusting comprises cinching the coronary sinus.
19. The method of claim 13 further comprising selecting a therapy device and securing the therapy device to the coronary sinus.
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US9301843B2 (en) 2003-12-19 2016-04-05 Boston Scientific Scimed, Inc. Venous valve apparatus, system, and method
US9918834B2 (en) 2004-09-02 2018-03-20 Boston Scientific Scimed, Inc. Cardiac valve, system and method
US8932349B2 (en) 2004-09-02 2015-01-13 Boston Scientific Scimed, Inc. Cardiac valve, system, and method
US9622859B2 (en) 2005-02-01 2017-04-18 Boston Scientific Scimed, Inc. Filter system and method
US9808341B2 (en) 2005-02-23 2017-11-07 Boston Scientific Scimed Inc. Valve apparatus, system and method
US9370419B2 (en) 2005-02-23 2016-06-21 Boston Scientific Scimed, Inc. Valve apparatus, system and method
US9861473B2 (en) 2005-04-15 2018-01-09 Boston Scientific Scimed Inc. Valve apparatus, system and method
US8672997B2 (en) 2005-09-21 2014-03-18 Boston Scientific Scimed, Inc. Valve with sinus
US8460365B2 (en) 2005-09-21 2013-06-11 Boston Scientific Scimed, Inc. Venous valve, system, and method with sinus pocket
US9474609B2 (en) 2005-09-21 2016-10-25 Boston Scientific Scimed, Inc. Venous valve, system, and method with sinus pocket
US8348999B2 (en) 2007-01-08 2013-01-08 California Institute Of Technology In-situ formation of a valve
US8133270B2 (en) 2007-01-08 2012-03-13 California Institute Of Technology In-situ formation of a valve
US8470023B2 (en) 2007-02-05 2013-06-25 Boston Scientific Scimed, Inc. Percutaneous valve, system, and method
US9421083B2 (en) 2007-02-05 2016-08-23 Boston Scientific Scimed Inc. Percutaneous valve, system and method
US8414641B2 (en) 2007-12-21 2013-04-09 Boston Scientific Scimed, Inc. Valve with delayed leaflet deployment
US9668859B2 (en) 2011-08-05 2017-06-06 California Institute Of Technology Percutaneous heart valve delivery systems
US9744037B2 (en) 2013-03-15 2017-08-29 California Institute Of Technology Handle mechanism and functionality for repositioning and retrieval of transcatheter heart valves

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CA2587930A1 (en) 2006-06-15 application
US20060129051A1 (en) 2006-06-15 application
US7211110B2 (en) 2007-05-01 grant
US7806928B2 (en) 2010-10-05 grant
US20070168023A1 (en) 2007-07-19 application
EP1827316A1 (en) 2007-09-05 application
CN101072546A (en) 2007-11-14 application
JP2008522749A (en) 2008-07-03 application
CN101072546B (en) 2011-11-02 grant

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