US20080312676A1 - Device And Kit For Treatment Of Disorders In The Heart Rhythm Regulation System - Google Patents

Abstract

A tissue cutting device is disclosed, which is structured and arranged to be inserted through the vascular system into a body vessel adjacent to the heart and/or into the heart, and to be subsequently subjected to a change of shape in order to penetrate into the heart tissue. The tissue cutting device may thus be used for treating disorders to the heart rhythm regulation system. A kit of devices provides a plurality of devices for creating a lesion pattern for treating such disorders.

Description

RELATED APPLICATIONS
• This application claims priority to International Application No. PCT/EP2005/005363 filed May 17, 2005 entitled A Device And Kit For Treatment Of Disorders In The Heart Rhythm Regulation System which is hereby incorporated by reference.
FIELD OF THE INVENTION
• The present invention relates to treatment of disorders in the heart rhythm regulation system and, specifically, to a tissue cutting device, a kit of shape-changing devices and a method for treating such disorders.
BACKGROUND OF THE INVENTION
• The circulation of blood in the body is controlled by the pumping action of the heart. The heart expands and contracts by the force of the heart muscle under impulses from the heart rhythm regulation system. The heart rhythm regulation system transfers an electrical signal for activating the heart muscle cells.
• The normal conduction of electrical impulses through the heart starts in the sinoatrial node, travels across the right atrium, the atrioventricular node, the bundles of His and thereafter spread across the ventricular muscle mass. Eventually when the signal reaches the myocytes specialized in only contraction, the muscle cell will contract and create the pumping function of the heart (seeFIG. 1).
• The electrical impulses are transferred by specially adapted cells. Such a cell will create and discharge a potential over the cell membrane by pumping ions in and out of the cell. Adjacent cells are joined end-to-end by intercalated disks. These disks are cell membranes with a very low electrical impedance. An activation of a potential in a cell will propagate to adjacent cells thanks to the low impedance of the intercalated disks between the cells. While being at the embryonic stage, all heart muscle cells, the myocytes, have the ability to create and transfer electrical signals. During evolution the myocytes specialize and only those cells necessary for maintaining a stable heart-rate are keeping the ability to create and send electrical impulses. For a more thorough explanation of the propagation of electrical signals in the heart, see e.g. Sandöe, E. and Sigurd, B.,Arrhythmia, Diagnosis and Management, A Clinical Blectrocardiographic Guide, Fachmed AG, 1984.
• The heart function will be impaired if there is a disturbance on the normal conduction of the electrical impulses. Atrial fibrillation (AF) is a condition of electrical disorder in the heart rhythm regulation system. In this condition, premature and fast signals irregularly initiating muscle contractions in the atria as well as in the ventricles will be started in ectopic sites, that is areas outside the sinoatrial node. These signals will be transmitted erratically all over the heart. When more than one such ectopic site starts to transmit, the situation becomes totally chaotic, in contrast to the perfect regularity in a healthy heart, where the rhythm is controlled from the sinoatrial node.
• Atrial fibrillation is a very common disorder, thus 5% of all patients that undergo heart surgery suffer from AF. 0.4-2% of a population will suffer from AF, whereas 10% of the population over the age of 65 suffers from AF. 160,000 new cases occur every year in the US and the number of cases at present in the US is estimated to be around 3 million persons. Thus, treatment of atrial fibrillation is an important topic.
• Typical sites for ectopic premature signals in AF may be anywhere in the atria, in the pulmonary veins (PV), in the coronary sinus (CS), in the superior vena cava (SVC) or in the inferior vena cava (IVC). There are myocardial muscle sleeves present around the orifices and inside the SVC, IVC, CS and the PVs. Especially around the orifice of the left superior pulmonary vein (LSPV) such ectopic sites are frequent, as well as at the orifice of the right superior pulmonary vein (RSPV). In AF multiple small circles of a transmitted electrical signal started in an ectopic site may develop, creating re-entry of the signal in circles and the circle areas will sustain themselves for long time. There may be only one ectopic site sending out signals leading to atrial flutter, or there may be multiple sites of excitation resulting in atrial fibrillation. The conditions may be chronic or continuous since they never stop. In other cases there may be periods of normal regular sinus rhythm between arrhythmias. The condition will then be described as intermittent.
• In the chronic or continuous cases, the atrial musculature undergoes an electrical remodelling so that the re-entrant circuits sustain themselves continuously. The patient will feel discomfort by the irregular heart rate, sometimes in form of cannon waves of blood being pushed backwards in the venous system, when the atria contract against a closed arterio-ventricle valve. The irregular action of the atria creates standstill of blood in certain areas of the heart, predominantly in the auricles of the left and right atrium. Here, blood clots may develop. Such blood clots may in the left side of the heart get loose and be taken by the blood stream to the brain, where it creates disastrous damage in form of cerebral stroke. AF is considered to be a major cause of stroke, which is one of the biggest medical problems today.
• Today, there are a few methods of treating the problems of disorders to the heart rhythm regulation system. Numerous drugs have been developed to treat AF, but the use of drugs is not effective to a large part of the patients. Thus, there has also been developed a number of surgical therapies.
• Surgical therapy was introduced by Drs. Cox, Boineau and others in the late 1980s. The principle for surgical treatment is to cut all the way through the atrial wall by means of knife and scissors and create a total separation of the tissue. Subsequently the tissues are sewn together again to heal by fibrous tissue, which does not have the ability to transmit myocardial electrical signals. A pattern of cutting was created to prohibit the propagation of impulses and thereby isolate the ectopic sites, and thus maintain the heart in sinus rhythm. The rationale for this treatment is understandable from the description above, explaining that there must be a physical contact from myocyte to myocyte for a transfer of information between them. By making a complete division of tissue, a replacement by non-conductive tissue will prohibit further ectopic sites to take over the stimulation. The ectopic sites will thus be isolated and the impulses started in the ectopic sites will therefore not propagate to other parts of the heart.
• It is necessary to literally cut the atria and the SVC and the IVC in strips. When the strips are sewn together they will give the impression of a labyrinth guiding the impulse from the sinoatrial node to the atrioventricular node, and the operation was consequently given the name Maze. The cutting pattern is illustrated inFIG. 2 and was originally presented in J L Cox, T E Canavan, R B Schuessler, M E Cain, B D Lindsay, C Stone, P K Smith, P B Corr, and J P Boineau,The surgical treatment of atrial fibrillation. II. Intraoperative electrophysiologic mapping and description of the electrophysiologic basis of atrial flutter and atrial fibrillation, J Thorac Cardiovasc Surg, 1991 101:406-426. The operation has a long-time success of curing patients from AF in 90% of the patients. However, the Maze operation implicate that many suture lines have to be made and requires that the cuts are completely sealed, which is a demanding task for every surgeon that tries the method. The operation is time consuming, especially the time when the patients own circulation has to be stopped and replaced by extracorporeal circulation by means of a heart-lung machine. Thus mortality has been high and the really good results remained in the hands of a few very trained and gifted surgeons.
• The original Maze operation has therefore been simplified by eliminating the number of incisions to a minimum, still resulting in a good result in most cases. The currently most commonly used pattern of incisions is called Maze III (seeFIG. 3).
• Other methods of isolating the ectopic sites have also been developed recently. In these methods, the actual cutting and sewing of tissue has been replaced by methods for killing myocyte cells. Thus, one may avoid separating the tissue, instead one destroy the tissue by means of heat or cooling in the Maze pattern to create a lesion through the heart wall. The damaged myocyte tissue can not transfer signals any more and therefore the same result may be achieved. Still the chest has to be opened, and the heart stopped and opened. Further, the energy source has to be carefully controlled to affect only tissue that is to be destroyed.
• A large number of devices have now been developed using various energy sources for destroying the myocyte tissue. Such devices may use high radio frequency energy, as disclosed in e.g. U.S. Pat. No. 5,938,660, or microwaves, ultrasound or laser energy. Recently, devices have been developed for catheter-based delivery of high radio frequency energy through the venous and or arterial systems. However, this has so far had limited success due to difficulties in navigation and application of energy and also late PV stenosis has been reported. Further, devices using cooling of tissue has used expanding argon gas or helium gas to create temperatures of −160° C. Using an instrument with a tip, tissue can be frozen and destroyed.
• WO03/003948 discloses an apparatus for treating, preventing, and terminating arrhythmias. The device, which is implanted and left at the target site, is provided with protrusions that pierce the tissue, via self-expansion or balloon expansion, to gain access to the cells of said target site. The protrusions are used to conduct drugs to the cells, which drugs may cause cell death to thereby induce cellular changes that may lead to treatment of arrhythmias. Nowhere in WO03/003948 is a device described that by expansion fully penetrates the wall of the blood vessel to disrupt cardiac impulses, which device then is bio-absorbed and thereby eliminated from the target site. The device according to WO03/003948 is not a cutting device.
OBJECTS AND SUMMARY OF THE INVENTION
• Accordingly, the present invention seeks to mitigate, alleviate or eliminate one or more of the above-identified deficiencies and to provide a new device, and kit of devices, suitable for a method for treatment of disorders to the heart rhythm regulation system of the kinds referred to, according to the appended independent claims.
• For this purpose a tissue cutting device according to claim1 is provided, wherein the device is of an at least partly spherical shape and structured and arranged to be inserted in a temporary delivery shape through the vascular system into a body vessel adjacent to the heart and/or into the heart and to be subsequently subjected to a change of shape, from said temporary delivery shape via an expanded delivered shape to a further expanded shape, extending at least beyond an inner surface of said tissue, in order to create cutting action configured for cutting said heart tissue and/or said body vessel.
• Advantageous features of the invention are defined in the dependent claims.
BRIEF DESCRIPTION OF THE DRAWINGS
• The invention will now be described in further detail by way of example under reference to the accompanying drawings, on which:
• FIG. 1 is a schematic view of the transmission of electrical signals in the heart;
• FIG. 2 is a schematic view of a pattern of cutting tissue of the heart wall according to the Maze-procedure for treating disorders to the heart rhythm regulation system;
• FIG. 3 is a schematic view of a simplified pattern according to the Maze III-procedure, wherein the heart is seen from behind;
• FIGS. 4a-4care perspective schematic views of a tissue cutting device according to an embodiment of the invention, whereinFIG. 4ashows the tissue cutting device in a first, temporary shape,FIG. 4bshows the tissue cutting device in a second, permanent shape, andFIG. 4cillustrates the tissue cutting device having sharp edges;
• FIGS. 5a-5bshow the tissue cutting device ofFIGS. 4a-4binserted in a body vessel;
• FIGS. 6-14 show different embodiments of the tissue cutting device;
• FIG. 15 shows a tissue cutting device comprising a cutting arm according to an embodiment of the invention, the tissue cutting device being shown inserted into a vessel with the cutting arm extending into a heart atrium before the tissue cutting device has started acting on the heart wall tissue;
• FIG. 16 shows the tissue cutting device ofFIG. 15 during the time when the cutting arm penetrates a heart wall and the tissue cutting device penetrates tissue at the orifice of a vessel;
• FIG. 17ashows the tissue cutting device ofFIG. 15 after the tissue cutting device has penetrated the heart wall and the vessel wall at the orifice area and has completed a change of shape;
• FIG. 17bshows the tissue cutting device ofFIG. 15 after the device has penetrated the heart wall and has completed a change of shape similarly toFIG. 17a, but where the cutting arm of the device abuts another tissue cutting device inserted into another vessel;
• FIG. 17cis a schematic view showing the tissue cutting device ofFIG. 15 after it has completed its change of shape, wherein the tissue lesion creating device has been inserted into the left superior pulmonary-vein and the cutting arm is extended to the left atrial appendage opening;
• FIG. 17dis a perspective view with a section of the vessel and the heart wall cut-off and shows the tissue cutting device ofFIG. 15 after the device has penetrated the heart wall and has completed a change of shape similarly toFIG. 17a, but where the tissue cutting device comprises an atrial end instead of the cutting arm;
• FIGS. 18-25 are schematic views of the heart showing tissue cutting devices inserted into different blood vessels adjacent the heart and illustrating cutting patterns achieved by these tissue lesion creating devices, whereinFIGS. 18-19 and24-25 show a cross-section that has been cut through the atria of the heart andFIGS. 20-23 show the atria of the heart from the outside of the heart seen from behind;
• FIGS. 26a-26bshows a cross-section of the left atrial appendage and a tissue cutting device inserted into the left atrial appendage, whereinFIG. 26ashows the tissue cutting device before a change of shape has started andFIG. 26bshows the tissue cutting device after the change of shape;
• FIGS. 27-28 illustrate tissue cutting devices inserted into the left atrial appendage and the right atrial appendage, the figures showing a cross-section that has been cut through the atria of the heart;
• FIGS. 29-31 illustrate three different embodiments of accessing the vascular system;
• FIG. 32 illustrates a guide wire being inserted into the coronary sinus;
• FIG. 33 illustrates a guide wire being inserted into the coronary sinus and a guide catheter being inserted with its tip at the orifice of the coronary sinus;
• FIG. 34 is a view similar toFIG. 33 showing a first tissue cutting device being inserted into the coronary sinus;
• FIGS. 35 and 36 illustrate a guide wire having been inserted into the left atrium;
• FIGS. 37-39 illustrate the carrying and deployment of a tissue cutting device by means of a delivery catheter;
• FIGS. 40-42 illustrate the deployment of a tissue cutting device in the left superior pulmonary vein;
• FIGS. 43-46 illustrate the insertion of a tissue cutting device into the inferior and superior vena cava;
• FIG. 47 illustrate the deployment of a tissue cutting device according toFIG. 14 in the left atrium;
• FIG. 48 illustrate the deployment of a tissue cutting device according toFIG. 14 in the right atrium; and
• FIG. 49 illustrate a tissue lesion creating cutting device according toFIG. 14alocated in the left atrium.
DETAILED DESCRIPTION OF THE INVENTION
• Referring now toFIGS. 1-3, the problems of disorders to the heart rhythm regulation system and the leading current method of treating these problems will be described. InFIG. 1, aheart2 is shown and the controlling of the heart rhythm is indicated. The heart rhythm is normally controlled from the sinoatrial node4. The sinoatrial node4 transmits electrical signals which are propagated through the heart wall by means of special cells forming an electrical pathway. The electrical signals following the electrical pathway will coordinate the heart muscle cells for almost simultaneous and coordinated contraction of the cells in a heart atrium and heart ventricle. The normal conduction of electrical impulses through the heart starts in the sinoatrial node4, travels across the right atrium, theatrioventricular node5, the bundles of His6 and thereafter spread across the ventricular muscle mass. In a disordered situation, electrical signals are started in heart cells outside the sinoatrial node4, in so called ectopic sites. These electrical signals will disturb the coordination of the heart muscle cells. If several ectopic sites are present, the signal transmission becomes chaotic. This will be the cause of arrhythmic diseases, such as atrial fibrillation and atrial flutter.
• An existing method for treating these diseases is based on isolating the ectopic sites in order to prevent the electrical signals started in these ectopic sites to propagate in the heart wall. Thus, the heart wall is cut completely through for interrupting the coupling between cells that transmit erratic electrical signals. The thus created lesion will be healed with fibrous tissue, which is unable to transmit electrical signals. Thus, the path of the electrical signals is blocked by this lesion. However, since the location of the ectopic sites may not always be known and may be difficult to determine or since there might be multiple ectopic sites, a special cutting pattern has been developed, which will effectively isolate ectopic sites. Thus, the same pattern may always be used regardless of the specific locations of the ectopic sites in each individual case. The procedure is called the “Maze”-procedure in view of the complicated cutting pattern. InFIG. 2, the Maze-pattern is illustrated.
• However, as is evident fromFIG. 2, the cutting pattern is extensive and complex and requires a difficult surgery. Thus, the Maze-pattern has been evolved in order to minimize the required cuttings and simplify the pattern as much as possible. Currently, a Maze III-pattern is used, as shown inFIG. 3. This pattern is not as complicated, but would still effectively isolate the ectopic sites in most cases. The Maze III-pattern comprises acut8 around the left superior pulmonary vein (LSPV) and the left inferior pulmonary vein (LIPV) and acorresponding cut10 around the right superior pulmonary vein (RSPV) and the right inferior pulmonary vein (RSPV); acut12 connecting the twocuts8 and10 around the pulmonary veins (PV); acut14 from this connecting cut to the coronary sinus (CS); acut16 from the left PVs to the left atrial appendage; acut18 from the inferior vena cava (IVC) to the superior vena cava (SVC); acut20 connecting thecut10 around the right PVs and thecut18 between the IVC and the SVC; acut22 from thecut18 between the IVC and the SVC along the right lateral atrium wall; and acut24 isolating the right atrial appendage. Thus, a pattern, which is less complex and which effectively isolates the ectopic sites, has been established. In some cases, all cuts may not be needed. For example, the occurrence of ectopic sites often starts around the orifices of the PVs and, therefore, it may be sufficient to make thecuts8,10 around the PVs. Further, as indicated with thelines8′ and10′, the cuts around the PVs may be done along each PV orifice instead of in pairs.
• According to the invention, there is provided a possibility of cutting through the heart wall in a new manner. Thus, a similar pattern to the Maze III-pattern should also be achieved according to this new manner. However, as mentioned above, it may not in all cases be required that all cuts of the Maze III-pattern are made.
• Referring now toFIGS. 4-5, a heart wall tissue lesion creating cuttingdevice26 according to an embodiment of the invention will be described and the new manner of performing the cuts through the heart wall will be explained. The heart wall tissue lesion creating cutting device26 (hereinafter called cutting device) is shown inFIG. 4ain a first state, in which thecutting device26 is tubular and has a first diameter d. The cuttingdevice26 is shown inFIG. 4bin a second state, in which thecutting device26 is tubular and has a second diameter D, which is larger than the first diameter d. The cuttingdevice26 is formed of a shape memory material, which has the ability of memorizing a permanent shape that may significantly differ from a temporary shape. The shape memory material will transfer from its temporary to its memorized, permanent shape as a response to a suitable stimulus. The stimulus may be exposure to a raised temperature, such as a temperature above e.g. 30° C. that may be caused by the body temperature. The stimulus may suitably be combined with the release of a restraining means, which may keep the shape memory material from assuming its permanent shape.
• The shape memory material allows designing acutting device26 that may be contracted into a small, temporary shape before insertion into a patient. Thus, the cuttingdevice26 may be inserted in this temporary shape to the heart of a patient through the vascular system. The temporary shape of the cuttingdevice26 is also flexible, whereby guiding thecutting device26 through the vascular system is facilitated. This insertion of the cuttingdevice26 may be performed with well-known percutaneous catheter techniques. This is an unaggressive procedure and may be performed on a beating heart. Thus, the cuttingdevice26 may readily be positioned at a desired position within the vascular system adjacent heart wall tissue to be treated. The cuttingdevice26 may then be allowed to transfer to its memorized, permanent shape when inserted to the desired position in a blood vessel.
• As shown inFIG. 5a, the cuttingdevice26 is inserted in its temporary shape in a desired position within ablood vessel28. As a response to a stimulus, e.g. the body temperature, the cuttingdevice26 will then strive towards changing its shape and obtaining the permanent shape. The memorized, permanent shape of the cuttingdevice26 will not fit into theblood vessel28, whereby the cuttingdevice26 will force itself through surrounding tissue for obtaining the permanent shape, as shown inFIG. 5b. In this way, the cuttingdevice26 will first penetrate the vessel wall and thereafter tissue surrounding theblood vessel28. Tissue cells that are penetrated will be killed, which will start a healing reaction in the body. Where thecutting device26 is placed in a desired position to change shape through heart wall tissue, cells that are able to transmit electrical signals may thus be killed. The healing process will not restore the ability to transmit electrical signals and, therefore, the cuttingdevice26 will reduce the ability of transmitting electrical signals through the heart wall. By placing several cutting devices intelligently and designing the permanent shape of thecutting devices26 accordingly, thecutting devices26 may penetrate heart wall tissue to create a pattern of cuts corresponding to the Maze III-pattern. An example of a shape memory material, is Nitinol, which is an alloy composed of nickel (54-60%) and titanium. Small traces of chrome, cobalt, magnesium and iron may also be present. This alloy uses a martensitic phase transition for recovering the permanent shape. Shape memory materials may also be formed of shape memory polymers, wherein the shape-memory effect is based on a glass transition or a melting point. Such shape memory polymers may be produced by forming polymers of materials or combinations of materials having suitable properties. For example, a shape memory polymer may be created of oligo(e-caprolactone) dimethacrylate combined with n-butyl acrylate. Also, biodegradable or bioresorbable materials may be used for forming these shape memory polymers. In this way, the cuttingdevice26 may be designed such that it will be degraded or absorbed by the body after it has performed its change of shape. For example, a polylactic acid polymer and/or a polyglycolic acid polymer, poly (e-caprolactone) or polydioxanone may be used for forming a shape memory polymer that is biodegradable. A special feature of the resorbable shape memory polymers is that these will disappear from the tissue after having had its function, limiting potential negative effects of otherwise remaining polymer or Nitinol materials, such as perforations and damage to other adjacent tissues, like lungs, oesophagus and great vessels like the aorta.
• The cuttingdevice26 may alternatively be formed to exhibit an elasticity such that it has a strive towards its permanent shape. This may be accomplished by forming the cuttingdevice26 to a spiral-shape in e.g. stainless steel or a magnesium alloy which is biodegradable.
• The cuttingdevice26 may be tubular in both its temporary shape and its permanent shape, as shown inFIGS. 4-5. However, the shape memory may be used for bringing the cuttingdevice26 between any shapes. Some examples of shapes that are at least not entirely tubular will be given below. The shape of the cuttingdevice26 in its first state is preferably compact to facilitate insertion of the cuttingdevice26 through the vascular system. Thus, a tubular shape is suitable, but other shapes may be just as suitable. Further, the shape of the cuttingdevice26 in its second state is designed such that the change of shape will provide penetration of specific heart tissue in order to block propagation of undesired electrical signals. Also, the shape of the cuttingdevice26 in its second state may be adjusted for fixing the cuttingdevice26 to its desired position within the body.
• The cuttingdevice26 may be constructed of a net; i.e. its shape may comprise meshes or loops. This implies that a solid surface need not penetrate tissue, whereby the penetration through tissue and the forming of different shapes of the cuttingdevice26 will be facilitated.
• The edges of the cuttingdevice26 facing the tissue to be penetrated may be made especially sharp to increase its effectiveness, as illustrated inFIG. 4c. Another feature is to cover the surface towards the tissue to be penetrated with drugs that increase the cutting effect or prohibit the thickening of the wall of the vessel in which the device is inserted. Examples of such drugs are ciclosporin, taxiferol, rapamycin, tacrolimus, alcohol, glutaraldehyde, formaldehyde, and proteolytic enzymes like collagenase. Collagenase is effective in breaking down tissue and especially fibrin tissue, which is otherwise difficult to penetrate. Therefore, covering the surface of the cuttingdevice26 with collagenase would particularly speed up the process of penetrating tissue. The drugs are attached to the surface of the cuttingdevice26 according to well-known methods of attaching drugs to medical devices. One such method is embedding drugs into or under layers of polymers, which cover the surface. Of course, other methods may be used. Similarly, drugs preventing thrombosis and increasing in-growth of endothelium on the endothelial surface after penetration of the cuttingdevice26 may be attached to thecutting device26. Such drugs would be e.g. Endothelium Growth Factor, and Heparin. Also, other drugs designed to treat arrhythmias may be attached to the cutting device surface. Such drugs are e.g. amiodarone and sotalol.
• Preferably, the inside of the cuttingdevice26 inserted into a blood vessel will be in contact with the blood stream inside the blood vessel. Such inside surface of the cuttingdevice26 may as well be covered with antithrombotic drugs. Such drugs would be e.g. Heparin, Klopidogrel, Enoxaparin, Ticlopidin, Abciximab, and Tirofiban.
• Another way to increase the effectiveness of the cuttingdevice26 is to attach a metallic part of the cuttingdevice26 to electrical currency, which would provide a heating of the cuttingdevice26. Thereby, tissue may also be killed by this heating, enhancing the effect of the cuttingdevice26. Further, the force driving the change of shape will also be increased, speeding up the shape change of the cutting device.
• Referring now toFIGS. 6-12, cutting devices that are specifically suited for insertion into specific blood vessels will be described. All or some of these cutting devices may be delivered in a kit to be used for treatment of a disorder of the heart rhythm regulation system. Alternatively, the cutting devices may be delivered separately. Then, the required cutting devices for an operation may be assembled for each specific patient or for a specific disease pattern. The cutting devices may also be provided in different sizes to suit the size of the heart and the vessels of the patient. Thus, a complete kit is assembled from devices designed to fit to the anatomical conditions of the actual treatment locations in order to achieve optimal results.
• Referring now toFIG. 6, afirst cutting device30 adapted to be inserted into the CS is shown. Thisfirst cutting device30 has atubular part32, which is pre-bent to assume a curved shape to fit to the curvature of the CS. Thus, thefirst cutting device30 will assume a curved temporary shape within the CS. Further, the cross-section of thefirst cutting device30 is smaller in a distal end34 to be inserted furthest into the CS than at aproximal end36 to be placed at the orifice of the CS. The cross-section of thefirst cutting device30 may be elliptic or circular or may vary along the length of the cuttingdevice30. Thefirst cutting device30 may be designed to change shape such that the cross-section of thefirst cutting device30 is mainly expanded at the inside of the curve towards the heart wall. Thus, thefirst cutting device30 will penetrate the heart wall tissue adjacent the CS. Moreover, thefirst cutting device30 has a length of at least the distance between the two inferior PVs. It can also be designed to cover the distance from the orifice of the CS and past the LIPV. Thefirst cutting device30 may serve as support for other cutting devices inserted into other blood vessels adjacent the heart, as explained in more detail later on. In this case, it may suffice that thefirst cutting device30 is fixated into the CS wall. There may also not be any need for thefirst cutting device30 penetrating heart tissue itself, when treating the PV orifices solely. Thefirst cutting device30 may also comprise one or more cutting arms (not shown), which, in the temporary shape of thefirst cutting device30, extend along thetubular part32 or in an axial direction of thetubular part32. Further, thefirst cutting device30 may be arranged to change shape such that the one or more cutting arms extend in a radial direction from thetubular part32. Thus, during the change of shape, the one or more cutting arms will penetrate through heart tissue adjacent the CS.
• Referring now toFIGS. 7a-b, asecond cutting device38 adapted to be inserted into the LIPV is shown. InFIG. 7a, thesecond cutting device38 is illustrated in a contracted, temporary shape, and inFIG. 7b, thesecond cutting device38 is illustrated in an expanded state. Thissecond cutting device38 is adapted to be inserted at the orifice of the LIPV into the heart. Thesecond cutting device38 has atubular part40. As shown inFIGS. 7a-b, thetubular part40 may comprise two or more portions. Afirst portion42 of thetubular part40 to be inserted closest to the LIPV orifice is arranged to change shape to circumferentially penetrate the LIPV wall and penetrate heart wall tissue around the LIPV. Thus, an effective block against propagation of undesired electrical signals is created around the orifice of the LIPV. Asecond portion44 of thetubular part40 is arranged to change shape to abut the vessel wall or only penetrate into the vessel wall. Thus, thissecond portion44 will only serve to stabilize thesecond cutting device38 in the axial direction and it may not be needed. The first42 andsecond portions44 of thetubular part40 are interconnected by a connectingmember46, in the form of bars or wires. Thefirst portion42 may be funnel-shaped having a larger diameter at the end closest to the orifice of the LIPV. The funnel-shape will partly compensate for the increasing diameter of the LIPV towards the orifice. However, the diameter of the funnel-shapedfirst portion42 may increase to a larger extent than the LIPV towards the orifice, whereby thesecond cutting device38 will penetrate deeper into the heart tissue at the orifice end. Further, the smaller end of the funnel-shapedfirst portion42 may be arranged to merely penetrate into or abut the vessel wall for stabilizing thesecond cutting device38 in its axial direction. Thefirst portion42 of thetubular part40 may extend from the orifice of the LIPV inside the heart to a position outside the heart wall, whereby the smaller end of the funnel-shaped first portion is arranged outside the heart wall. Thus, thefirst portion42 may still penetrate through heart tissue throughout the entire thickness of the heart wall, even though the smaller end of the funnel-shaped first portion merely penetrates into or abuts the vessel wall.
• Thetubular part40 is typically arranged to change shape to penetrate a circular area of tissue around and adjacent the LIPV. However, thetubular part40 may also be arranged to change shape to expand to such a degree that it would come in contact with thefirst cutting device30 inserted into the CS, whereby the heart tissue between the LIPV and the CS will be effectively treated. Then, the first30 and thesecond cutting devices38 in contact with each other will stabilize each other's positions.
• The end of thetubular part40 forms anatrial end48, which is arranged to be inserted extending into the heart atrium when thesecond cutting device38 is inserted into its desired position. Thus, as shown inFIG. 7a, during insertion of thesecond cutting device38, theatrial end48 will extend in an axial direction of thetubular part40. However, when thesecond cutting device38 changes shape theatrial end48 will be folded outwardly extending in a radial direction to thetubular part40, as shown inFIG. 7b. Theatrial end48 will during its change of shape penetrate into the heart wall for fixing the position of thesecond cutting device38 and for forming a block against undesired electrical signals around the orifice of the LIPV. Thisatrial end48 may be formed of, for instance, a multiple of arches overlapping each other. Each such arch will penetrate through a piece of tissue adjacent the LIPV orifice and leave a small islet of separated tissue, after having penetrated through the tissue.
• Thesecond cutting device38 may also comprise a cuttingarm50. The cuttingarm50 is attached to the end of thetubular part40 to be inserted closest to the LIPV orifice. In the temporary shape of thesecond cutting device38, as shown inFIG. 7a, the cuttingarm50 extends in an axial direction of thetubular part40 for facilitating insertion of thesecond cutting device38. In the permanent shape of thesecond cutting device38, the cuttingarm50 extends in a radial direction of thetubular part40, as shown inFIG. 7b. When thesecond cutting device38 is placed in its desired position, the cuttingarm50 will extend into the heart atrium. Thus, during the change of shape of thesecond cutting device38, the cuttingarm50 will penetrate through the heart wall tissue to assume a position extending radially from thetubular part40. This effect of the cuttingarm50 will be explained in more detail below with reference toFIGS. 14-16. The cuttingarm50 will create a line blocking propagation of undesired electrical signals in the heart wall. Thus, the cuttingarm50 could make cutting lines for forming the desired cutting pattern. The cuttingarm50 of thesecond cutting device38 may be arranged to make a cut from the LIPV to the CS. Thus, the cuttingarm50 could come in contact with thefirst cutting device30 inserted into the CS, which would fixate the position of the cuttingarm50. This cuttingarm50 could also comprise atrough52 in the portion of the cuttingarm50 that will contact thefirst cutting device38. This ensures that the cuttingarm50 beyond thetrough52 may extend through the heart wall from the CS to the mitral valve. Thesecond cutting device38 may also have further cutting arms (not shown) to be extended towards any of the other PVs.
• The cutting arm is constructed of sequential loops in a longitudinal direction of the arm. As these loops penetrate through the heart wall tissue, closed loops of lesion lines will be formed, creating islets of untreated tissue inside them. The lesion lines will present a block of propagation of electrical signals.
• In another embodiment of the present invention, according toFIG. 8, the tubular part may also comprise two segments connected to each other axially where the first part, closest to the left atrium, is considerably larger in diameter than the second, deeper part that is supposed to fit into a smaller branch of the pulmonary vein system. Thus this embodiment would look like a pair of trousers with one leg cut of in the groin area. In this embodiment the smaller segment in the deeper smaller vein would give excellent support for the larger part closest to the ostium of the pulmonary vein, prohibiting this part to migrate into the left atrium, according toFIG. 8b. This embodiment may naturally also comprise theatrial end48 and the cuttingarm50, according toFIG. 8c. The tubular part may comprise at least two axially separated tubular portions, which are interconnected by a connecting member. These tubular portions may then be structured and arranged to change shape to expand to different diameters or be transversely expandable to different degrees. This may be used for the same purpose as the funnel-shape described above. Thus, at least one of the tubular portions may be structured and arranged to change shape to expand its diameter to correspond to the diameter of the vessel where it is placed. In this way, this tubular portion will only serve to keep the device in place. Another tubular portion may then change shape to penetrate the heart tissue for the treatment purposes, further, the connecting member may be one or more bars or wires connecting the tubular portions.
• Referring now toFIG. 9, athird cutting device54 adapted to be inserted into the RIPV is shown. Thisthird cutting device54 presents similar features as thesecond cutting device38. Thus, thethird cutting device54 also comprises atubular part56, which also may consist of two or moretubular portions58,60, which are interconnected by a connectingmember62. Thetubular part56 of thethird cutting device54 presents similar features as thetubular part40 of thesecond cutting device38. Thethird cutting device54 also comprises anatrial end64, similar to theatrial end48 of thesecond cutting device38. Moreover, thethird cutting device54 also comprises a cuttingarm66, similar to the cuttingarm50 of thesecond cutting device38. This cuttingarm66 is arranged to change shape in order to extend radially from thetubular part56 towards the CS and come in contact with thefirst cutting device30 inserted into the CS close to the orifice of the CS. The cuttingarm66 of thethird cutting device54 is normally shorter than the cuttingarm50 of thesecond cutting device38 permitting adaptation to the different distance between thethird cutting device54 and the CS. Further, the cuttingarm66 of thethird cutting device54 need not have a trough, since, in this case, there is no need of treating heart tissue beyond the CS. Thethird cutting device54 may also comprise other cutting arms (not shown) extending towards any of the other PVs.
• Referring now toFIG. 10, afourth cutting device68 adapted to be inserted into the LSPV is shown. Thisfourth cutting device68 presents similar features as the second andthird cutting devices38,54. Thus, thefourth cutting device68 also comprises atubular part70, which may consist of two or moretubular portions72,74, which are interconnected by a connectingmember76. Thetubular part70 of thefourth cutting device68 presents similar features as thetubular part40,56 of the second andthird cutting devices38,54. Thefourth cutting device68 also comprises anatrial end78, similar to theatrial end48,64 of the second andthird cutting devices38,54. Moreover, thefourth cutting device68 also comprises a cuttingarm80, similar to the cuttingarm66 of thethird cutting device54. This cuttingarm80 is arranged to change shape in order to extend radially from thetubular part70 towards the LIPV and come in contact with thesecond cutting device38 inserted into the LIPV. The cuttingarm80 of thefourth cutting device68 is normally very short permitting adaptation to the short distance between the LSPV and the LIPV, which is typically a few millimeters to a centimeter. Thefourth cutting device68 may also comprise another cutting arm (not shown), which after the change of shape of thefourth cutting device68 would extend towards the left atrium appendage orifice.
• Referring now toFIG. 11, afifth cutting device82 adapted to be inserted into the RSPV is shown. Thisfifth cutting device82 presents similar features as the second, third andfourth cutting devices38,54,68. Thus, thefifth cutting device82 also comprises a tubular part84, which may consist of two or moretubular portions86,88, which are interconnected by a connectingmember90. The tubular part84 of thefifth cutting device82 presents similar features as thetubular part40,56,70 of the second, third andfourth cutting devices38,54,68. Thefifth cutting device82 also comprises anatrial end92, similar to theatrial end48,64,78 of the second, third andfourth cutting devices38,54,68. However, thefifth cutting device82 would normally not comprise any cutting arm, since it would normally be sufficient to penetrate the tissue around the RSPV. Thefifth cutting device82 may anyhow comprise a cutting arm adapted to extend towards any of the other PVs.
• Referring now toFIG. 12, asixth cutting device94 adapted to be inserted into the left atrial appendage (LAA) or the right atrial appendage (RAA) is shown. Thesixth cutting device94 comprises atubular part96, which has an elliptic cross-section to fit into the elliptic form of the orifice of the LAA. Asixth cutting device94 adapted to be inserted into the RAA will have atubular part96 with a less elliptic cross-section to fit the orifice of the RAA. Thesixth cutting device94 is adapted to be inserted into the orifice of the LAA inside the left atrium or into the orifice of the RAA inside the right atrium. Thesixth cutting device94 will further change shape by expanding itstubular part96 through the atrial wall at the orifice. Thus, the LAA or the RAA will be completely cut off from electrical contact with the rest of the heart tissue. Thetubular part96 of thesixth cutting device94 may be quite short extending from the orifice of the atrial appendage along its wall into the atrial appendage. Further, thetubular part96 may be funnel-shaped, whereby a portion of thetubular part96 may be designed to change shape in order to assume a cross-section that will not penetrate through the entire heart wall. This portion of thetubular part96 may then serve to keep thesixth cutting device94 in place. Further, another portion of thetubular part96 will penetrate through the entire heart wall in order to effectively electrically isolate the atrial appendage from the rest of the heart. Asixth cutting device94 adapted to be inserted into the LAA may comprise a cutting arm (not shown), which is adapted to change shape to penetrate through the heart tissue extending from the LAA to afourth cutting device68 inserted into the LSPV. Further, asixth cutting device94 adapted to be inserted into the LAA may comprise afilm98 covering an end of thetubular part96 to be inserted closest to the orifice of the LAA. When thetubular part96 is expanded into the heart wall, thefilm98 will cover the orifice of the LAA, excluding the LAA from the blood circulating through the heart, whereby a dislocation of thrombus and clot formation in the LAA will be avoided.
• Referring now toFIG. 13a, aseventh cutting device100 adapted to be inserted into the IVC and the SVC is shown. Theseventh cutting device100 comprises twopieces102,104, afirst piece102 to be inserted into the SVC and asecond piece104 to be inserted into the IVC. Eachpiece102,104 of theseventh cutting device100 comprises atubular part106,108, which presents similar features as thetubular part40,56,70,84 of the second, third, fourth, andfifth cutting devices38,54,68,82. Eachtubular part106,108 may advantageously be funnel-shaped, wherein an end having the largest cross-section is adapted to be inserted closest to the orifice of the IVC or the SVC, respectively. Theseventh cutting device100 further comprises a connectingcutting arm110. Theseventh cutting device100 is arranged to change shape such that this connecting cuttingarm110 will extend between thetubular part106 of thefirst piece102 inserted into the SVC and thetubular part108 of thesecond piece104 inserted into the IVC. This change of shape will cause the connectingcutting arm110 to penetrate through the lateral right atrium heart wall tissue between the orifice of the SVC and the orifice of the IVC. The connectingcutting arm110 may be attached to any one of the first and thesecond piece102,104 of theseventh cutting device100, and preferably the connectingcutting arm110 is attached to both the first and thesecond pieces102,104. If the connectingcutting arm110 is only attached to one of the first andsecond pieces102,104, it will connect the first and thesecond pieces102,104 together after the change of shape has occurred. The connectingcutting arm110 may comprise abranch112, which, after the change of shape of theseventh cutting device100, will extend from a point of the connectingcutting arm110 laterally through the right atrial wall, whereby thisbranch112 will penetrate the right lateral wall of the right atrium. As for the cutting arms, thebranch112 may be constructed of one loop or several sequential loops in a longitudinal direction of thebranch112. Theseventh cutting device100 may comprise a further cutting arm (not shown), which may be attached to thetubular part108 of thesecond piece104 that is inserted into the IVC. Theseventh cutting device100 is then arranged to change shape such that this further cutting arm will extend from thetubular part108 of thesecond piece104 inserted into the IVC towards and into the orifice of the CS. This change of shape will cause the further cutting arm to penetrate through the heart wall tissue between the orifice of the IVC and CS. This further cutting arm may alternatively be arranged as a further branch of the connectingcutting arm110. Theseventh cutting device100 may, in a simple version for treating mild forms of disorders to the heart rhythm regulation system, consist of only thefirst piece102 adapted to be inserted into the SVC, whichfirst piece102 may or may not comprise a cutting arm. As shown inFIG. 13b, the first andsecond pieces102,104 may also each comprise anatrial end103,105, similar to theatrial end48,64,78,92 of the second, third, fourth, andfifth cutting devices38,54,68,82.
• In still another embodiment the heart tissue cutting device is located inside the atrium to be treated. The device then would be made out of at least one thread or wire, according toFIGS. 14atof. If the atrial device is made out of more than one wire the wires would be interconnected or braided to each other. In one of the embodiments the implanted shape of the device will assume a net-like pattern. Further the net-like pattern may form a shape that is arranged to encompass at least a portion of the atrium it is intended to treat before cutting through the wall. The net-like pattern may form a spherical form encompassing a substantial part of the atrium, according toFIG. 14a. The net-like pattern may form an ellipsoidal segment, according toFIGS. 14btod, encompassing a substantial part of the atrium. Again the net-like pattern may form a cup-shape. Thus the device is adapted to be positioned in the upper or lower part of the atrium. The atrial device would be formed identical to at least a part of the inner surface of the atrium, only considerably larger, allowing the device to grow through the entire wall of the heart, to come outside of the atrium and thereby cutting the atrium in peaces. The cut made will be replaced continuously by scar tissue that does not conduct electrical signals. Thus, islets of atrial wall tissue containing tissue that conduct electrical signals are isolated unable to transmit erratic current to the next islet.
• In the embodiment according toFIG. 14athe cutting device according to the present invention may be in form of a globulus. This globulus is placed inside the heart, such as in the left or right atrium, in a temporary shape. The cutting device is then stimulated, by for example temperature, according to above, to expand towards its memorized, permanent shape. This expansion results in that the heart tissue is cut by the cutting device according to the present invention. Tissue cells that are penetrated by the cutting device will be killed, which will start a healing reaction in the body. Where the cutting device is placed in a desired position to change shape through heart wall tissue, cells that are able to transmit electrical signals may thus be killed. The healing process will not restore the ability to transmit electrical signals and, therefore, the cutting device will reduce the ability of transmitting electrical signals through the heart wall.
• The cutting devices according toFIG. 14 may also be combined with the tubular parts of all other embodiments of the present invention, i.e. the cutting devices according toFIG. 14 may be connected with different kinds of tubular parts. These tubular parts may then for example be delivered in a body vessel adjacent the heart while the cutting device according to any ofFIG. 14 is delivered inside the heart.
• Referring now toFIGS. 15-17, the action of a cutting arm will be explained in further detail. InFIG. 15, acutting device114 comprising acutting arm116 has been inserted into a blood vessel at the orifice of the opening into the heart. Thecutting device114 comprises atubular part118, which is inserted into the blood vessel. The cuttingarm116 is attached to thetubular part118 and extends into the heart. InFIG. 15, thecutting device114 is shown in an intermediate shape, which it has during insertion of thecutting device114. Thecutting device114 has carried to the illustrated position on acatheter113awhile being restrained by a restrainingsheath113b. Thecutting device114 is shown when thetubular part118 has been released while thecutting arm114 is still restrained by the restrainingsheath113b. Thus, a change of shape has not yet been fully commenced. InFIG. 16, thecutting device114 is shown during its action of changing its shape. Thus, the cuttingarm116 is extending from the inside of the heart into the heart wall tissue having penetrated heart tissue during the shape-change. The cuttingarm116 will continue penetrating heart tissue in order to obtain the permanent shape of thecutting device114. InFIG. 17a, thecutting device114 is shown after having completed its change of shape. Thetubular part118 has now cut through the vessel wall and penetrated heart tissue around the vessel. Further, the cuttingarm116 is now completely outside the heart. Thus, the cuttingarm116 has now penetrated the entire heart wall and has therefore caused a lesion along a cutting line from the orifice of the blood vessel wall through the selected adjacent heart wall. The penetrated tissue is marked with shading inFIG. 17a, as well as inFIGS. 17b-d. InFIG. 17b, the cuttingarm116 of thecutting device114 is shown abutting anothercutting device120, which has been inserted into another blood vessel. In this way, the cuttingarm116 has performed a lesion between the two cutting devices, whereby an effective block against propagation of undesired electrical signals has been created. The position of the cuttingarm116 is also stabilized after the change of shape by the cuttingarm116 resting on theother cutting device120. In,FIG. 17c, thecutting device114 is shown inserted into the LSPV, and thecutting arm116 has been extended leaning into the orifice of the LAA and thereby penetrating the atrial wall between the LAA. and the LSPV. In addition to the cutting of the cuttingarm116, thetubular part118 of thecutting device114 inserted inside the vessel has treated the vessel wall adjacent to the orifice, which often contains ectopic sites. InFIG. 17d, thecutting device114 is shown comprising anatrial end121, which has penetrated the tissue around the orifice of the blood vessel.
• Referring now toFIGS. 18-28, there is shown cutting patterns being obtained in a few different embodiments, illustrating a few examples of sets of cutting devices being inserted into blood vessels adjacent the heart and the treatment obtained by these sets of cutting devices. The treatment needed may differ from patient to patient and other patterns may be conceivable using the concept of inserting cutting devices into blood vessels adjacent the heart. InFIG. 18, the first, second, third, fourth andfifth cutting devices30,38,54,68,82 having been inserted into the four PVs are shown. Thecutting devices30,38,54,68,82 are shown in an intermediate shape, which they present shortly after having been delivered to the desired positions and before any penetration of heart wall tissue has begun. Thetubular parts40,56,70,84 of the second, third, fourth andfifth cutting devices38,54,68,82 have expanded to abut the wall of its respective PV. The cutting arms of the second, third, fourth andfifth cutting devices38,54,68r82 have been diverted from the axial direction of the tubular part to abut the inside of left atrial wall of the heart. Thesecond cutting device38 inserted into the LIPV is shown having a cuttingarm50 extending to the mitral valve. Thethird cutting device54 inserted into the RIPV has a cuttingarm66 extending to the CS. Thus, instead of forming thecuts12 and14 according toFIG. 3, cuts are formed from the LIPV and the RIPV to the CS. Thesecuts12 and14 are very difficult to accomplish using the technique of inserting cutting devices into the blood vessels. However, these cuts may be replaced by the more easily accomplished cutting pattern formed by thearms50 and66 in combination with a cut formed by thefirst device30 inserted into the CS when expanded out of the CS. Thus, with thearms50 and66 in direct contact with thefirst cutting device30 inserted in the CS, the same effect as from thecuts12 and14 inFIG. 3 is achieved. Thesecond cutting device38 inserted into the LIPV is further shown having a cutting arm extending to the LSPV. Thethird cutting device54 inserted into the RIPV is further shown having a cutting arm extending to the RSPV. Thefourth cutting device68 inserted into the LSPV is shown having a cuttingarm80 extending to the LAA. Thefifth cutting device82 inserted into the RSPV is shown having a cutting arm extending to thefourth cutting device68. The cutting arms of thecutting devices38,54,68,82 may be arranged in any desired combination between the cuttingdevices38,54,68,82 forming connections between the cuttingdevices38,54,68,82. However, the cutting arms may also be arranged freely, without necessarily having contact to another cutting device.
• InFIG. 19, the cutting devices shown inFIG. 18 are shown after the change of shape of the devices has occurred. Now, the second, third, fourth andfifth cutting devices38,54,68,82 have expanded out of the respective PVs and the treated tissue around the orifices of the PVs is shown in shading. Further, the cutting arms have penetrated the heart tissue and have created cutting lines between the PVs, from the LIPV to the mitral valve, from the LSPV to the CS, and from the LSPV to the LAA orifice.
• InFIGS. 20-23, different embodiments of theseventh cutting device100 inserted into the SVC and the IVC is shown. InFIG. 20, the first andsecond pieces102,104 of theseventh cutting device100 are shown being inserted at the orifices of the SVC and the IVC. The first andsecond pieces102,104 will treat the heart tissue around the orifices of the SVC and the IVC, respectively. InFIG. 21, thesecond piece104 is shown comprising acutting arm122, which extends from the orifice of the IVC into the orifice of the CS, whereby the cuttingarm122 penetrates heart tissue of the right atrium free wall. InFIG. 22, theseventh cutting device100 is shown comprising the connectingcutting arm110, which extends between thefirst piece102 inserted into the SVC and thesecond piece104 inserted into the IVC. The connectingcutting arm110 will penetrate heart tissue in the right lateral aspect and the right lateral to posterior aspect of the right atrial wall. InFIG. 23, theseventh cutting device100 is shown comprising abranch112 of the connectingcutting arm110. Thebranch112 extends from a point on the connectingcutting arm110 laterally, creating a vertical cut outwards in the lateral right atrium wall. Alternatively, thisbranch112 may be arranged as a further cutting arm extending from thefirst piece102 inserted into the SVC.
• InFIGS. 24-25, the cutting devices according to the present invention are shown inserted into the CS, the PVs and the IVC and the SVC, respectively. The cutting devices are shown in an intermediate state corresponding to the state shown inFIG. 18. BothFIGS. 24 and 25 illustrate cutting arms between the PVs and from the LIPV past thefirst cutting device30 in the CS extending to the mitral valve. Thus, thefirst cutting device30 inserted in the CS provides a support for the cutting arms extending from the PVs for stabilizing the position of the cutting arms after the change of shape of the cutting devices has been completed. Thefirst cutting device30 inserted into the CS has, at least partly, an elliptic cross-section enabling thefirst cutting device30 to penetrate tissue close to the mitral valve. Also, there is a cuttingarm122 extending from the IVC to the orifice of the CS. InFIG. 24, there is shown the connectingcutting arm110 between the SVC and the IVC, whereas this connecting cutting arm is not present inFIG. 25. The cutting patterns shown inFIGS. 24 and 25 illustrate cutting patterns that will effectively block propagation of undesired electrical signals in the heart tissue for most patients suffering from disorders to the heart rhythm regulation system. Thus, inserting cutting devices to create these cutting patterns may effectively treat most patients suffering from disorders to the heart rhythm regulation system. However, these cutting patterns do not illustrate treatment of the atrial appendages, as will be shown inFIGS. 26-28. It should be appreciated that the cutting pattern ofFIGS. 24 and 25 may be supplemented with this treatment of the atrial appendages. InFIGS. 26-28, there is shown thesixth cutting devices94 inserted into the LAA and the RAA. As shown inFIGS. 26a-bin cross-section, thesixth cutting device94 is inserted at the orifice of the appendage (FIG. 26a) and expanded at this position to penetrate through the heart wall (FIG. 26b). Thesixth cutting device94 has an elliptic cross-section to fit to the shape of the appendage. InFIG. 27,sixth cutting devices94 are shown inserted into the LAA and the RAA. Thesixth cutting device94 inserted into the LAA is shown having a cuttingarm124 extending to the LSPV, and thesixth cutting device94 inserted into the RAA is shown having a cutting arm extending along the lateral right atrium wall. InFIG. 28, thesixth cutting device94 is shown inserted into the LAA. This sixth cutting94 device has no cutting arm; instead afourth cutting device68 inserted into the LSPV is shown having a cuttingarm80 extending to the LAA. Thesixth cutting device94 inserted into the LAA has a film ormembrane98 covering an end of itstubular part96 at the LAA orifice. This film ormembrane98 will exclude the LAA from blood contact with the rest of the heart and thereby prohibit migration of thrombus or clot formation from the LAA to, for instance, the brain.
• Now, a system for delivery of a cutting device into a desired position in a blood vessel adjacent the heart will be described. Each cutting device may be inserted into its desired position using such a delivery system. The delivery system allows a precise placement of each cutting device into the heart and the big vessels of the body. The delivery system has a restraining device, which keeps the cutting device in its temporary shape. This allows insertion into the blood vessel through catheters having a small bore, making minimal trauma to the patient. The restraining device may be a restraining tube, into which the cutting device is forced in its temporary shape. By cooling the cutting device, in case of a cutting device made of Nitinol, it may be easier to force the cutting device into the restraining tube. Once inserted into the desired position, the cutting device may be pushed out of the restraining tube by means of a piston or the cutting device may be released by retracting the restraining tube from its position over the cutting device. In case of a cutting device made of Nitinol, the cutting device may also be restrained by cooling to prevent it from obtaining a transition temperature trigging the change of shape. Thus, the cutting device may be restrained by cooling during insertion into the desired position and released by suspension of the cooling when inserted at the desired position. In WO 03/022179, such a delivery system is described in more detail.
• Now, a method for treating a patient having a disorder to the heart rhythm regulation system will be described. The patient is prepared for operation and operation is performed in an environment allowing visualization of the heart and the attached big vessels using fluoroscopy and ultrasound according to conventional techniques.
• The operation is started by making a puncture of a vein providing an access point to the vascular system of the patient according to conventional techniques. Usually, the femoral vein in the groin, as illustrated inFIG. 29, the subclavian vein on the chest, or the internal or external jugular vein on the neck, as illustrated inFIG. 30, is used. However, other smaller veins may be used instead. Also, in difficult cases when the pulmonary veins cannot be accessed from the vein, arterial access through the femoral artery in the groin may be used, as illustrated inFIG. 31. This method will, however, not be further discussed here. A delivery system is used for inserting the above described cutting devices into blood vessels adjacent the heart. First, anintroducer sheath130 of the delivery system is inserted at the puncture providing an access route into the vascular system. Then, a diagnostic catheter of the delivery system is inserted through theintroducer sheath130 into the vascular system. The diagnostic catheter is manoeuvred through the vascular system into the CS. Next, aguide wire132 of the delivery system is inserted through a channel of the diagnostic catheter into the CS and all the way to the vein parallel to the left anterior descending artery of the heart, close to the apex of the heart. Theguide wire132 is inserted as far as possible into the vascular system to be firmly positioned. Thereafter, the diagnostic catheter is withdrawn from the patient. Theguide wire132 will then extend from outside the patient into the patient via the access point and inside the patient to the CS, as illustrated inFIG. 32.
• Aguide catheter134 of the delivery system is now inserted over theguide wire132 so that theguide catheter134 is positioned with its tip at the orifice of the CS, as illustrated inFIG. 33. Now, there is aguide wire132 extending from the outside of the patient and theguide catheter134, through theguide catheter134, through the CS, the great cardiac vein and the anterior vein parallel to the LAD all the way to the apex of the heart.
• Referring toFIG. 34, adelivery catheter136 of the delivery system for carrying thefirst cutting device30 into the desired position has a guide wire channel throughout its length. The end of theguide wire132 outside the patient is then inserted into the guide wire channel of thedelivery catheter136, whereby thedelivery catheter136 may be inserted over theguide wire132 and inside theguide catheter134 into the CS. Thedelivery catheter136 has an inner part providing the guide wire channel and carrying the cutting device at a distal portion. Thedelivery catheter136 may further comprise an outer, restraining part, which covers the cutting device and keeps it in a contracted, temporary state. The restraining part may be axially displaceable in relation to the inner part. Thus, the restraining part may be retracted for releasing the cutting device. In this way, thefirst cutting device30 is inserted into the CS and may be located in its desired position. A correct position is when the distal end34 of thefirst cutting device30 is positioned within the CS beyond the LIPV next to the CS and theproximal end36 of thefirst cutting device30 is closer to the orifice of the CS than the RIPV. Preferably, thefirst cutting device30 extends all the way to the orifice of the CS. Without moving thefirst cutting device30 away from its correct position, thefirst cutting device30 is released from the delivery catheter. Thefirst cutting device30 will then immediately expand radially until contact is established with the CS wall, as illustrated inFIG. 34. Thereafter, thedelivery catheter136 is withdrawn from the patient.
• However, thefirst cutting device30 is arranged to change shape to assume a shape having much larger diameter than the natural diameter of the CS. Thus, thefirst cutting device30 will expand to its designed, permanent shape and the CS wall will not be able to prevent thefirst cutting device30 from obtaining its permanent shape. In order to obtain its permanent shape, thefirst cutting device30 will therefore penetrate tissue in the path of the change of shape. In this way, thefirst cutting device30 will expand to penetrate the heart tissue outside the CS, for instance the left atrium wall. The penetrated tissue will be killed and replaced by fibrous tissue, which is not able to transmit electrical signals. Thus, a block against propagation of undesired electrical signals may be created in this manner.
• As an option, thefirst cutting device30 may be inserted into the CS in a first separate session of the treatment of a patient. Thus, thisfirst cutting device30 may be allowed to be well-anchored in the tissue around the CS, before other cutting devices are inserted. This is suitable since some of the other cutting devices are adapted to contact thefirst cutting device30 inserted into the CS in order to stabilize and fix their positions. Thefirst cutting device30 will be well-anchored within a few weeks, typically within three weeks. In this time thefirst cutting device30 has penetrated the tissue around the CS and is firmly embedded by the tissue fixing its position. Then, the patient will come back for a second session of the treatment. Thus, a puncture is again made into a vein for allowing access again to the vascular system. However, all the cutting devices may alternatively be inserted during one session.
• Now, aguide wire140 is advanced inside a diagnostic catheter into the left atrium (LA), as illustrated inFIGS. 35 and 36. In order to access the LA, the atrial septum between the LA and the right atrium (RA) must be penetrated. If the patient has a patent foramen ovale (PFO,FIG. 35), which is an opening between the LA and the RA that is normally only present during the fetal period in humans, this may be used and enlarged, for instance by means of a balloon catheter (not shown). If no PFO is present (FIG. 36), asmall opening142 must first be created by means of a long flexible needle passed through a diagnostic catheter inside the access vein. Again, theopening142 in the atrial septum may be enlarged by means of a balloon. Once the needle is inside the LA, the catheter is passed over the needle into the LA and the needle is retracted. Aguide wire140 may now be advanced through the catheter into the LA and further into the LIPV.
• Referring now toFIGS. 37-39, the release of a cutting device will be generally described. Thus, having now placed theguide wire140, thesecond cutting device38 may be inserted to its desired position using a guide catheter extending to the LIPV orifice and adelivery catheter144, as illustrated inFIG. 37, in a similar manner as for the insertion of thefirst cutting device30. Thedelivery catheter144 has aninner part146 providing the guide wire channel. Thetubular part40 of thesecond cutting device38 is arranged in front of theinner part146 such that theinner part146 of thedelivery catheter144 pushes thetubular part40 in front of it. Thedelivery catheter144 may further comprise an outer, restrainingpart148, which covers the cutting device and keeps it in a contracted, temporary state. The restrainingpart148 may be axially displaceable in relation to theinner part146. Thus, the restrainingpart148 may be retracted for releasing the cuttingdevice38. Thedelivery catheter144 has a marker on the catheter outside the patient, as well as ax-ray marker149 visible on the fluoroscopy, indicating securely the orientation of the cuttingarm50 of thesecond cutting device38. Thesecond cutting device38 is now rotated into a position where it will change shape in such a way that the cuttingarm50 will extend to contact and be supported by thefirst cutting device30, which has been inserted previously. Thesecond cutting device38 is advanced into a position where theatrial end48 of thesecond cutting device38 is still outside the LIPV orifice. When the correct position of thesecond cutting device38 is confirmed by means of fluoroscopy and/or ultrasound, the distal end of thesecond cutting device38 is released from the delivery catheter far inside the PV, whereby the distal end will expand radially to fix the position of thesecond cutting device38. Next, a mid portion of thesecond cutting device38 and theatrial end48 is released, as illustrated inFIG. 38. Now, the cuttingarm50 is released, as illustrated inFIG. 39, and allowed to assume its radial extension from thetubular part40, whereby it will penetrate the heart wall to contact thefirst cutting device30.
• Now, theguide wire140 is retracted into the LA. The diagnostic catheter is inserted again and guided into the RIPV, whereby theguide wire140 may be inserted into the RIPV. Thereafter, the diagnostic catheter is withdrawn from the patient. Then, thethird cutting device54 is inserted using a guide catheter extending to the RIPV orifice and adelivery catheter144 in a manner similar to the insertion of thesecond cutting device38. Thus, the orientation of the cuttingarm66 of thethird cutting device54 is determined in the same manner as for thesecond cutting device38. Having correctly positioned thethird cutting device54, thetubular part56, theatrial end64 and the cuttingarm66 of thethird cutting device54 are released in a manner similar to the release of thesecond cutting device38. Now, the cuttingarm66 is released and allowed to assume its radial extension from thetubular part56, whereby it will penetrate the heart wall to contact thefirst cutting device30.
• Thereafter, theguide wire140 is again retracted into the LA and inserted into the LSPV, as illustrated inFIG. 40. Then, thefourth cutting device68 is inserted using aguide catheter150 extending to the LSPV orifice and adelivery catheter144, as illustrated inFIG. 41, in a manner similar to the insertion of the second andthird cutting devices38,54. Thus, the orientation of the cuttingarm80 of thefourth cutting device68 is determined in the same manner as for the second andthird cutting devices38,54. Thefourth cutting device68 may have two cutting arms, which are adapted to extend towards thesecond cutting device38 and towards the LAA. Having correctly positioned thefourth cutting device68, thetubular part70, theatrial end78 and the one or two cuttingarms80 of thefourth cutting device68 are released in a manner similar to the release of the second andthird cutting devices38,54, as further illustrated inFIG. 42. Now, the cutting arms are released and allowed to assume their radial extension from thetubular part70, whereby they will penetrate the heart wall to contact thesecond cutting device38 or extend to the orifice of the LAA, respectively.
• Again, theguide wire140 is retracted into the LA and inserted into the RSPV. Then, thefifth cutting device82 is inserted using aguide catheter150 extending to the RSPV orifice and adelivery catheter144 in a manner similar to the insertion of the second, third andfourth cutting devices38,54,68. Usually, thefifth cutting device82 has no cutting arm and therefore only the axial position of thefifth cutting device82 needs to be determined. Having correctly positioned thefifth cutting device82, the tubular part84, and theatrial end92 of thefifth cutting device82 are released in a manner similar to the release of the second, third, andfourth cutting devices38,54,68.
• Once again, theguide wire140 is retracted into the LA and now inserted into the LAA. Then, thesixth cutting device94 is inserted using aguide catheter150 extending to the LAA orifice and adelivery catheter144 in a manner similar to the insertion of the other cutting devices. Thesixth cutting device94 is advanced into a position where the entiresixth cutting device94 is inside the LAA, and a proximal end of thesixth cutting device94 is adjacent to the LAA orifice. Thedelivery catheter144 has a marker on the catheter outside the patient, as well as ax-ray marker149 visible on the fluoroscopy, indicating securely the orientation of thesixth cutting device94 such that the elliptic shape of thesixth cutting device94 may be oriented in correspondence to the elliptic shape of the LAA. When the correct position of thesixth cutting device94 is confirmed by means of fluoroscopy, a distal end of thesixth cutting device94 is released from the delivery system far inside the LAA, whereby the distal end will expand radially towards the wall of the LAA to fix the position of thesixth cutting device94. Next, a mid portion of thesixth cutting device94 and a proximal end are released. Now, thesixth cutting device94 is allowed to change its shape to cut through the heart wall of the LAA.
• Now, theguide wire140 is retracted from the LA into the RA and inserted into the RAA. Then, anothersixth cutting device94 is inserted using aguide catheter150 extending to the RAA orifice and adelivery catheter144 in a manner similar to the insertion of the other cutting devices. The othersixth cutting device94 is advanced into a position where the entiresixth cutting device94 is inside the RAA, and a proximal end of thesixth cutting device94 is adjacent to the RAA orifice. The position of thesixth cutting device94 is determined in a manner similar to the positioning of thesixth cutting device94 inserted into the LAA. When the correct position of thesixth cutting device94 is confirmed, thesixth cutting device94 inserted into the RAA is released in a manner similar to the release of thesixth cutting device94 inserted into the LAA. Now, thesixth cutting device94 is allowed to change its shape to cut through the heart wall of the RAA.
• Next, theguide wire140 is retracted from the RAA into the RA. If the access point to the vascular system was created in the upper part of the body, theguide wire140 extends through the SVC into the RA. Then, theguide wire140 is further inserted into the IVC, as illustrated inFIG. 43. On the other hand, if the access point to the vascular system was created in the lower part of the body, theguide wire140 extends through the IVC into the RA. Then, theguide wire140 is further inserted into the SVC. Thereafter, theseventh cutting device100 is inserted using aguide catheter150, as illustrated inFIG. 44, and adelivery catheter144 in a manner similar to the insertion of the other cutting devices. Theseventh cutting device100 is placed in position in the IVC, SVC and the RA, as illustrated inFIG. 45. Thedelivery catheter152 carries theseventh cutting device100 on theinner part154 of thecatheter152. Theinner part154 comprisesstops156, which prevent theseventh cutting device100 from being axially displaced from theinner part154 during insertion of the device. Again, thecutting device100 is kept in a contracted, temporary state by means of a restrainingpart158. The correct orientation of theseventh cutting device100 is obtained in a manner similar to the positioning of the second, third andfourth cutting devices38,54,68. Theseventh cutting device100 has now been rotated into a position where it will change shape in such a way that its cutting arm or cuttingarms122 will extend in intended directions. Thus, theseventh cutting device100 may comprise acutting arm122 that extends towards the orifice of the CS and/or abranch112 that extends from the connectingcutting arm110 of theseventh cutting device100 towards the lateral wall of the RA. When the correct position of theseventh cutting device100 is confirmed by means of fluoroscopy, a distal end of theseventh cutting device100 in thedelivery catheter152 is released from thedelivery catheter152 in the IVC or SVC, depending on where the distal end of the delivery catheter is placed. Thereafter, the connectingcutting arm110 is released and finally a proximal end of theseventh cutting device100 is released, as illustrated inFIG. 46.
• Now, theguide wire140 and thedelivery catheter152 is retracted outside the patient, since all parts of the treatment kit have been implanted.
• On special indication, for instance when it is difficult to place the guide wire inside the PVs, an arterial access may be used instead. The insertion technique is identical, except that the access to the vascular system is achieved by puncture of an artery and that the cutting devices are delivered through the arterial system instead of through the venous system. After puncture of the artery, a catheter is advanced through the aorta and passed by the aortic valve into the left ventricle and finally into the LA. The guide wire is advanced into the desired PV and the insertion of the cutting device may then be achieved in the manner described above.
• Referring now toFIGS. 47aandb, the release of a cutting device, according toFIG. 14, into the left atrium will be generally described. Thus, having now placed theguide wire140, the cutting device according toFIG. 14 may be inserted to its desired position using a guide catheter extending to the LA and adelivery catheter114, as illustrated inFIG. 37, in a similar manner as for the insertion of thefirst cutting device30. Thedelivery catheter144 has aninner part146 providing the guide wire channel. The guiding catheter and the delivery catheter are advanced well into the LA so that when releasing the device into the LA the device gets contact with the wall furthest away, the guiding catheter is retracted into the RA and the restraining catheter is retracted towards the atrial septum causing the device to be released into the LA. The catheters and the guide wire are retracted to outside the patient.
• Now a release of the device in the RA is described. The guide wire is advanced into the IVC if the approach is from the neck and into the SVC if the approach is from the groin, according toFIGS. 48aandb. The delivery catheter is advanced to the most distant point where the atrial device is to be deploid, the restraining catheter is retracted towards the SVC or IVC respectively, causing the device to be released into the RA, according toFIG. 48b. The catheters and the guide wire are retracted to outside the patient.
• FIG. 49ashows the cutting device according toFIG. 14apositioned in the RA, andFIG. 49bshows the same cutting device in the permanent, expanded shape, i.e. when the wall of the RA has been cut. The cutting devices according to the present invention have now been released such that they may change their shapes to obtain their permanent shapes. During the change of shape, each cutting device will penetrate heart tissue in the path of the change of shape. Thus, the cutting devices will now create the cutting pattern intended for forming blocks against propagation of undesired electrical signals in the heart. After the cutting devices have made their change of shape, the needed effect of the cutting devices on the heart tissue is completed. Thus, if the cutting devices are made of resorbable shape memory polymers, the cutting devices will be resorbed a time after termination of the cutting procedure. This time for resorption can be set by determination of the different ingredients of polymers and also by means of external altering, for instance by means of x-ray radiation, ultrasound, electron beams, or light of a defined wavelength, setting the time of the polymers to be resorbed. However, the cutting devices may also be left in the body after the change of shape, or only some of the cutting devices may be resorbed.
• Hereinafter, some potential uses of the present invention are described:
• A method for treatment of disorders in the heart rhythm regulation system, said method comprising:
• inserting a tissue cutting device through the vascular system to a desired position in a body vessel, and providing a change of shape of the tissue cutting device at said desired position to penetrate heart tissue adjacent said body vessel.
• The method according to above, wherein said tissue cutting device is inserted into a desired position in the coronary sinus, in any of the pulmonary veins, in the superior vena cava, in the inferior vena cava, or in the left or right atrial appendage. The method

Claims (49)

1. A tissue cutting device configured to reduce undesired signal transmission in a heart tissue in order to treat atrial fibrillation,

wherein the device is structured and arranged to be inserted in a temporary delivery shape through the vascular system and at least partly be positioned into said atrium that is intended to be treated and to be subsequently subjected to a change of shape, from said temporary delivery shape via an expanded delivered shape to a further expanded shape, extending at least beyond an outer surface of said atrial tissue,

wherein said tissue cutting device is configured to create cutting action for cutting of said heart tissue including said atrium, and wherein said tissue cutting device is structured and arranged to penetrate a wall of said heart tissue by said cutting action, in such a manner that a cut of said tissue created by said cutting action is continuously replaced by scar tissue that does not conduct electrical signals to isolate ectopic sites of said heart tissue causing said atrial fibrillation.

2. The tissue cutting device according toclaim 1, wherein the device is adapted to be positioned in the upper or lower part of the left or right atrium.

3. The tissue cutting device according toclaim 1, wherein the device is of an at least partly spherical shape.

4. The tissue cutting device according toclaim 1, wherein the device is made out of at least one thread or wire.

5. The tissue cutting device according toclaim 4, wherein the device is made out of more than one wire, wherein the wires are interconnected or braided to each other.

6. The tissue cutting device according toclaim 1, wherein the device is formed in a net-like pattern to a shape that is arranged to encompass at least a portion of said atrium that it is intended to treat before cutting through a wall of said atrium.

7. The tissue cutting device according toclaim 6, wherein the net-like pattern forms a spherical form encompassing a substantial part of said atrium.

8. The tissue cutting device according toclaim 6, wherein the net-like pattern forms an ellipsoidal segment that is arranged to encompass a substantial part of said atrium.

9. The tissue cutting device according to any ofclaim 6, wherein the net-like pattern forms a cup-shape.

10. The tissue cutting device according toclaim 1, wherein the device is formed identical to at least a part of the inner surface of said atrium, only considerably larger, allowing the device to grow through the entire wall of the heart, to come outside of the atrium and thereby cutting said atrium in pieces, wherein said cut is configured to be replaced continuously by said scar tissue that does not conduct electrical signals, such that islets of atrial wall tissue containing tissue that conduct electrical signals are isolated unable to transmit erratic current to the next islet.

11. The tissue cutting device according toclaim 6, wherein the device is in form of a globulus arranged and configured to be placed inside said atrium.

12. The tissue cutting device according toclaim 1, wherein the tissue cutting device is arranged and configured to create a cutting pattern intended for forming blocks against propagation of undesired electrical signals in the heart.

13. The tissue cutting device according toclaim 1, wherein the device comprises a shape memory material configured for achieving said change of shape from a temporary delivery shape to an expanded delivered shape in said atrium of said heart.

14. The tissue cutting device according toclaim 13, wherein said shape memory material is a resorbable shape memory polymer.

15. The tissue cutting device according toclaim 14, wherein a time for resorption of the polymer is determinable by different ingredients of polymers.

16. The tissue cutting device according toclaim 14, wherein a time for resorption of the polymer is determinable by means of external altering, such as by means of K-ray radiation, ultrasound, electron beams, or light of a defined wavelength.

17. The tissue cutting device according toclaim 1, wherein the device is biodegradable.

18. The tissue cutting device according toclaim 1, wherein the device is combined with a tubular part.

19. The tissue cutting device according toclaim 18, wherein the tubular part of the device is structured and arranged to be inserted in a temporary delivery shape through the vascular system into a body vessel adjacent to the heart, and to be subsequently subjected to a change of shape, from said temporary delivery shape via an expanded delivered shape to a further expanded shape, extending at least beyond an outer surface of said tissue, in order to create said cutting action configured for cutting said heart tissue and/or said body vessel, wherein the tubular part of said device comprises a plurality of segments connected to each other in longitudinal direction of said tubular part of said device, wherein a first segment of said plurality of segments has a dimension in a direction perpendicular to said longitudinal direction of said tubular part of said device that is larger than that dimension of a second segment thereof, at least in said expanded delivered shape.

20. The tissue cutting device according toclaim 19, wherein the second segment is configured to fit in a branch of the pulmonary vein system having a smaller diameter than the first segment.

21. The tissue cutting device according toclaim 19, wherein said device further comprises at least one cutting arm being structured and arranged to initially extend substantially perpendicular to said longitudinal direction from the tubular part of said tissue cutting device in order to be inserted into a heart atrium wall and said cutting arm being structured and arranged to change shape to extend radially from the tubular part of said tissue cutting device.

22. The tissue cutting device according toclaim 21, wherein the at least one cutting arm has a form comprising at least one closed loop.

23. The tissue cutting device according to any ofclaim 19, wherein said body vessel, which the device is structured and arranged to be inserted into, is the coronary sinus.

24. The tissue cutting device according toclaim 1, wherein an outside surface of the device is provided with sharp edges.

25. The tissue cutting device according toclaim 1, wherein an outside surface of the device is provided with drugs.

26. The tissue cutting device according toclaim 27, wherein said drugs include drug adapted to increase a cutting effect through tissue.

27. The tissue cutting device according toclaim 26, wherein said drug adapted to increase a cutting effect is any one in the group of alcohol, glutaraldehyde, formaldehyde, and proteolytic enzymes.

28. The tissue cutting device according toclaim 27, wherein said proteolytic enzymes are collagenase.

29. The tissue cutting device according toclaim 25, wherein said drugs include a drug adapted to prohibit a thickening of a wall of the body vessel in which the device is inserted.

30. The tissue cutting device according toclaim 29, wherein said drug adapted to prohibit a thickening is any one in the group of ciclosporin, taxiferol, rapamycin and tacrolimus.

31. The tissue cutting device according toclaim 25, wherein said drugs include any one in the group of Endothelium Growth Factor, Heparin, and amiodarone, sotalol or any other antiarrythmic drug.

32. The tissue cutting device according toclaim 1, wherein said device has a net-like shape formed of closed loops.

33. The tissue cutting device according toclaim 1, wherein the device is at least partly bioresorbable.

34. The tissue cutting device according toclaim 1, wherein the device is made of a shape memory polymer.

35. The tissue cutting device according toclaim 1, wherein the device is connected to at least one transversally expandable tubular part.

36. A kit of shape-changing cutting devices, comprising at least one tissue cutting device according toclaim 1 for treatment of disorders in the heart rhythm regulation system, said kit comprising:

a plurality of shape-changing cutting devices, which each has a first delivery and a second delivered state, wherein each device in the first state has such dimensions as to be insertable to a desired position within the vascular system, and wherein each device is capable of changing shape to substantially the second state when located at said desired position, at least the tissue cutting device in the second state having an at least partly spherical shape, which strives to a diameter that is larger than the diameter of the heart tissue at the desired position, whereby the tissue cutting device will become embedded into the tissue surrounding the tissue cutting device at the desired position and destroy the tissue in order to prevent it from transmitting electrical signals,

wherein at least one of the shape-changing devices is adapted to be inserted to a desired position at the orifice of a pulmonary vein in the heart, and at least one of the shape-changing devices is adapted to be inserted to a desired position in the coronary sinus, wherein the complete kit is assembled from devices designed to fit to the anatomical conditions of the actual treatment locations and to create a cutting pattern of said tissue by cutting action of said devices, wherein the devices are arranged and configured to continuously replace the cuts by scar tissue that does not conduct electrical signals.

37. The kit according toclaim 36, wherein the cutting pattern is independent of specific locations of ectopic sites causing said disorders in the heart rhythm regulation system in each individual case.

38. The kit according toclaim 36, wherein the cutting pattern is substantially a Maze III-pattern, comprising a plurality of cuts chosen from:

a first cut (B) around the left superior pulmonary vein (LSPV) and the left inferior pulmonary vein (RSPV) and the right inferior pulmonary vein (RSPV);

a third cut (12) connecting the first cut (8) and the second cut (10) around the pulmonary veins (PV);

a fourth cut (14) from the third cut (12) to the coronary sinus (CS);

a fifth cut (16) from the left pulmonary veins to the left atrial appendage;

a sixth cut (18) from the inferior vena cava (IVC) to the superior vena cava (SVC);

a seventh cut (20) connecting the second cut (10) around the right pulmonary veins and the sixth cut (18) between the IVC and the SVC;

an eighth cut (22) from the sixth cut (18) between the IVC and the SVC along the right lateral atrium wall; and

a ninth cut (24) isolating the right atrial appendage.

39. The kit according toclaim 36, wherein one of the shape-changing devices is adapted to be inserted into the pulmonary vein and comprises an arm, which in the second state is arranged to contact another shape-changing device in the coronary sinus.

40. The kit according toclaim 39, wherein said arm comprises a trough in an area to come in contact with the shape-changing device in the coronary sinus.

41. The kit according toclaim 36, wherein at least one of the shape-changing devices is adapted to be inserted into the inferior vena cava.

42. The kit according toclaim 41, wherein at least one of the shape-changing devices is adapted to be inserted into the superior vena cava.

43. The kit according toclaim 42, wherein at least one of the shape-changing device that is adapted to be inserted into the superior vena cava and the shape-changing device that is adapted to be inserted into the inferior vena cava comprises an arm, which in the second state is arranged to form a connection between these shape-changing devices.

44. The kit according toclaim 36, wherein the kit comprises four shape-changing devices, each being adapted to be inserted into a respective pulmonary vein.

45. The kit according toclaim 44, wherein at least one of the shape-changing devices is adapted to be inserted into a pulmonary vein comprises an arm, which in the second state is arranged to contact the shape-changing device in another pulmonary vein.

46. The kit according toclaim 36, wherein at least one of the shape-changing devices is adapted to be inserted into the left atrial appendage,

47. The kit according toclaim 46, wherein the shape-changing device that is adapted to be inserted into the left atrial appendage comprises an arm, which in the second state is arranged to contact the shape-changing device in a pulmonary vein.

48. The kit according toclaim 46, wherein the shape-changing device that is adapted to be inserted into the left atrial appendage comprises a film, which covers an end of the tubular shape of the device in the second state.

49. The kit according toclaim 36, wherein at least one of the shape-changing devices is adapted to be inserted into the right atrial appendage.

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