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EP1890637A1 - Dispositif biodegradable servant au decoupage de tissus, trousse et methode destines au traitement de troubles au niveau du systeme de regulation du rythme cardiaque - Google Patents

Dispositif biodegradable servant au decoupage de tissus, trousse et methode destines au traitement de troubles au niveau du systeme de regulation du rythme cardiaque

Info

Publication number
EP1890637A1
EP1890637A1 EP06755236A EP06755236A EP1890637A1 EP 1890637 A1 EP1890637 A1 EP 1890637A1 EP 06755236 A EP06755236 A EP 06755236A EP 06755236 A EP06755236 A EP 06755236A EP 1890637 A1 EP1890637 A1 EP 1890637A1
Authority
EP
European Patent Office
Prior art keywords
cutting device
tissue
tissue cutting
shape
heart
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Withdrawn
Application number
EP06755236A
Other languages
German (de)
English (en)
Inventor
Jan Otto Solem
Stevan Nielsen
Ib Joergensen
Gerd Seibold
Bodo Quint
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Syntach AG
Original Assignee
Syntach AG
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from PCT/EP2005/005363 external-priority patent/WO2006122573A1/fr
Application filed by Syntach AG filed Critical Syntach AG
Priority to EP06755236A priority Critical patent/EP1890637A1/fr
Publication of EP1890637A1 publication Critical patent/EP1890637A1/fr
Withdrawn legal-status Critical Current

Links

Definitions

  • 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.
  • the signal reaches the myocytes specialized in only contraction, the muscle cell will contract and create the pumping function of the heart (see Fig. 1) .
  • Typical sites for ectopic premature signals in AF may be anywhere in the atria, in the pulmonary veins
  • 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 .
  • a tissue cutting device for this purpose, is provided, wherein 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/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, wherein said cutting device is biodegradable .
  • Fig. 1 is a schematic view of the transmission of electrical signals in the heart
  • Figs 5a-5b show the tissue cutting device of Figs 4a-4b inserted in a body vessel.
  • a heart 2 is shown and the controlling of the heart rhythm is indicated.
  • the heart rhythm is normally controlled from the sinoatrial node 4.
  • the sinoatrial node 4 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 node 4, travels across the right atrium, the atrioventricular node 5, the bundles of His 6 and thereafter spread across the ventricular muscle mass.
  • ectopic sites In a disordered situation, electrical signals are started in heart cells outside the sinoatrial node 4, 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.
  • 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.
  • the path of the electrical signals is blocked by this lesion.
  • 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.
  • the Maze-pattern is illustrated.
  • the cutting pattern is extensive and complex and requires a difficult surgery.
  • the Maze-pattern has been evolved in order to minimize the required cuttings and simplify the pattern as much as possible.
  • a Maze Ill- pattern is used, as shown in Fig. 3. This pattern is not as complicated, but would still effectively isolate the ectopic sites in most cases.
  • a heart wall tissue lesion creating cutting device 26 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 device 26 (hereinafter called cutting device) is shown in Fig. 4a in a first state, in which the cutting device 26 is tubular and has a first diameter d.
  • the cutting device 26 is shown in Fig.
  • the cutting device 26 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 a cutting device 26 that may be contracted into a small, temporary shape before insertion into a patient.
  • the cutting device 26 may be inserted in this temporary shape to the heart of a patient through the vascular system.
  • the temporary shape of the cutting device 26 is also flexible, whereby guiding the cutting device 26 through the vascular system is facilitated.
  • This insertion of the cutting device 26 may be performed with well-known percutaneous catheter techniques. This is an unaggressive procedure and may be performed on a beating heart.
  • the cutting device 26 may readily be positioned at a desired position within the vascular system adjacent heart wall tissue to be treated. The cutting device 26 may then be allowed to transfer to its memorized, permanent shape when inserted to the desired position in a blood vessel.
  • the cutting device 26 is inserted in its temporary shape in a desired position within a blood vessel 28.
  • the cutting device 26 will then strive towards changing its shape and obtaining the permanent shape.
  • the memorized, permanent shape of the cutting device 26 will not fit into the blood vessel 28, whereby the cutting device 26 will force itself through surrounding tissue for obtaining the permanent shape, as shown in Fig. 5b.
  • the cutting device 26 will first penetrate the vessel wall and thereafter tissue surrounding the blood vessel 28. Tissue cells that are penetrated will be killed, which will start a healing reaction in the body.
  • the cutting device 26 may penetrate heart wall tissue to create a pattern of cuts corresponding to the Maze Ill-pattern.
  • the cutting device may also be spherical and/or globular. This cutting device may present the advantage of being able to affect cutting action in all directions simultaneously .
  • 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.
  • shape memory polymers may be produced by forming polymers of materials or combinations of materials having suitable properties.
  • a shape memory polymer may be created of oligo ( ⁇ -caprolactone) dimethacrylate combined with n- butyl acrylate.
  • biodegradable or bioresorbable materials may be used for forming these shape memory polymers .
  • Such a biodegradable or bioresorbable material may for example be a polymer, a ceramic, or metallic material .
  • Biodegradable materials such as biodegradable polymers, have bonds which are fissionable under physiological conditions.
  • Biodegradableness is the term used if a material decomposes from loss of mechanical properties due to, or within, a biological system. An implant's external form and dimensions may in fact remain intact during the decomposition. This means that a cutting device, which is biodegradalbe, may also be able to perform cutting action by transforming from a temporary shape to a memory shape. What is meant with respect to degradation time, provided no additional quantifying data is given, is the time it takes for the complete loss of mechanical properties.
  • a particularly suitable biodegradable material provides for the polymer composite to exhibit a hydrolytically degradable polymer, in particular poly (hydroxy carboxylic acids) or the corresponding copolymers .
  • Hydrolytic degradation has the advantage that the rate at which degradation occurs is independent of the site of implantation since water is present throughout the system.
  • the polymer composite exhibit a biodegradable thermoplastic amorphous polyurethane-copolyester polymer network.
  • the polymer composite exhibit a biodegradable elastic polymer network, obtained from crosslinking of oligomer diols with diisocyanate . Having polymer composites be formed as covalent networks based on oligo( ⁇ - caprolactone) dimethacrylate and butylacrylate is a conceivable alternative thereto.
  • the invention claims both hydrolytically as well as enzymatically degradable polymer composites for the biodegradable polymers.
  • hydrolytic degradation has the advantage that the rate at which degradation occurs is independent of implant location. In contrast, local enzyme concentrations vary greatly. Given biodegradable polymets or materials, degradation can thus occur through pure hydrolysis, enigmatically- induced reactions or through a combination thereof.
  • Typical hydrolyzable chemical bonds for the polymer composites of the cutting device are amide, ester or acetal bonds.
  • Two mechanisms can be noted with respect to the actual degradation. With surface degradation, the hydrolysis of chemical bonds transpires exclusively at the surface. Because of the hydrophobic character, polymer degradation is faster than the water diffusion within the material. This mechanism is seen especially with poly (anhydrides) and poly (orthoesters) .
  • poly (hydroxy carboxylic acids) particularly significant especially to the present invention, such as poly (lactic acid) or poly (glycol acid), the corresponding copolymers respectively, polymer degradation transpires throughout the entire volume.
  • the step which determines the rate here is the hydrolytic fission of the bonds since water diffusion in the somewhat hydrophilic polymer matrix occurs at a relatively fast rate .
  • Decisive for the use of biodegradable polymers is that, on the one hand, they degrade at a controlled or variable speed and, on the other, that the products of decomposition are nontoxic .
  • polymer material resorption refers to the substance or mass degrading through to the complete removal of a material from the body by way of the natural metabolism. In the case of cutting devices of only one degradable polymer, resorption begins as of that point in time of the complete loss of the mechanical properties. Specification of the resorption time covers the period starting from implantation of the cutting device and running through to the complete elimination of the cutting device.
  • polyesters such as poly(lactic acid), poly(glycol acid), poly (3-hydroxybutyric acid), poly (4- hydroxyvalerate acid), or poly ( ⁇ -caprolactone) , or the respective copolymers, polyanhydrides synthesized from dicarboxylic acids, such as, for example, glutar, amber, or sebacic acid, poly(amino acids), or polyamides, such as, for example, poly (serine ester) or poly (aspartic acid) .
  • dicarboxylic acids such as, for example, glutar, amber, or sebacic acid
  • poly(amino acids) poly(amino acids)
  • polyamides such as, for example, poly (serine ester) or poly (aspartic acid)
  • Biodegradable cutting devices having shape memory properties are particularly effective in this regard.
  • this type of degradable cutting devic can be introduced into the body in compressed (temporary) form through a small incision and once in place, then assume the memory shape relevant to its application after being warmed by the body temperature, as has been described above. The cutting device will then degrade after a given interval of time, thereby doing away with the need for a second operation to remove it.
  • biodegradable polymers Based on the known biodegradable polymers, structural elements can be derived for the synthesizing of biodegradable shape memory polymers.
  • suitable crosslinks, which fix the permanent form, and network chains, which serve as switching elements could be selected such that, on the on hand, the switching temperature can be realized through the physiological conditions, and on the other, toxicological problems with respect to any products of decomposition are excluded.
  • suitable switching segments for biodegradable shape memory polymers can be selected based on the thermal properties of said degradable materials. Of particular interest in this regard is a thermal transition of the switching elements in the temperature range of between room temperature and body temperature.
  • biodegradable polymer segments can be selectively synthesized by varying the stochiometric relationship of the known starting monomers; and the molecular weight of the formed polymers in the range of from approx. 500 to 10000 g/mol .
  • Suitable polymer segments are e.g. poly( ⁇ - caprolactone) diols with melting temperatures between 46 and 64 0 C or amorphous copolyesters based on lactic and glycol acid with glass transition temperatures between 35 and 40 0 C.
  • the phase transition temperatures hereby; i.e. the melting or glass transition temperature of the polymer switching segments, can be further diminished by their chain length or by degradation of specific end groups.
  • the polymer switching elements thus customized can then be integrated into physical or covalent crosslinked polymer networks, yielding the selectively composed biodegradable shape-memory polymer material.
  • biodegradable thermoplastic amorphous polyurethane copolyester polymer networks having shape memory properties are used as the material for the cutting device.
  • the amorphous polyurethane copolyester polymer networks having shape memory properties as formed have a glass transition temperature T ⁇ between 48 and 66 0 C and exhibit a modulus of elasticity in extension of between 330 and 600 MPa, a tensile strength respectively of between 18.3 and 34.7 MPa. Heating these networks to approximately 2O 0 C above this switching temperature yields elastic materials which can be deformed 50-265% into a temporary shape. Cooling down to room temperature occasions the forming of deformed shape memory polymer networks which have a clearly higher modulus of elasticity in extension of from 770 to 5890 Mpa . Upon subsequent reheating to 7O 0 C, the examples of deformed specimens thereby produced retransform back into the permanent shape after approximately 300 seconds.
  • polyurethane copolyester polymer networks in an aqueous phosphate buffer decomposed fully at 37 0 C over a period of between approximately 80 and 150 days By optimizing the composition of the biodegradable switching segments, degradable polyurethane copolyester polymer networks having shape memory properties can be produced substantially faster, e.g. within 14 days. Similar biodegradable elastic shape memory polymer networks can be yielded from crosslinking of oligomer diols with diisocyanate, which have melting temperatures between 38 and 85 0 C and which are likewise suitable for the cutting device. Degradableness was also ultimately assessed, whereby for these polymers in an aqueous phosphate buffer at 37 0 C , a 50% loss of mass was seen after approximately 250 days.
  • the braiding is formed from a biodegradable shape memory polymer on covalent networks based on oligo ( ⁇ - caprolactone) dimethacrylate and butylacrylate . It has been seen that subsequent implantation, this polymer composite has no negative impacts on the wound healing process. Therefore, the wounds created by the cutting device may heal into a scar tissue, that may prevent unwanted signals to be transmitted.
  • the synthesis of such biodegradable shape memory polymers can follow from n-butylacrylate which, because of the low glass transition temperature of -55 0 C for pure poly(n- butylacrylate) , can be used as a segment forming component . Network synthesis ensues through photopolymerization .
  • the switching temperature and the mechanical properties of the covalent network can be controlled.
  • the molar mass of the oligo ( ⁇ -caprolactone) dimethacrylate varies between 2000 and 10000 g/mol and the n-butylacrylate content between 11 and 90 % (by mass) .
  • biodegradable covalent and physical polymer networks having shape memory effect as described above, can also be used as a matrix for a controlled active substance release.
  • biodegradable polyurethane multiblock copolymers having shape memory effect based on poly (p-dioxanone) and trimethylhexa-methylene diisocyanate as the diisocyanate .
  • the combination with the poly (lactid-co-glycolid) or poly ( ⁇ -caprolactone) switching segments yields multiblock copolymers having a switching temperature of 37 or 42 0 C, respectively.
  • the hydrolytic degrading of the polymers shows that the polymers based on poly ( ⁇ -caprolactone) degrading at a lesser rate.
  • 50 to 90% of the initial mass was still present after 266 days of hydrolysis while in the case of the poly (lactid-co-glycolid) polymers, 14 to 26% was detectable after only just 210 days.
  • biodegradable shape memory polymer networks can be synthesized from a combination of physical or covalent shape memory polymer networks, having biodegradable polymer segments .
  • Selectively choosing the components allows setting optimal parameters for each respective application, such as the mechanical properties, the deformability, the phase transition temperatures and, above all, the switching temperature, as well as the rate of polymer decomposition .
  • the invention claims all aforementioned biologically degradable (biodegradable) shape memory polymers as material for the cutting device.
  • the cutting device When the cutting device is degraded in a biological environment, such as in a human body, the cutting device will start to elute substances . These substances are parts of the material that the cutting device is made of. If the cutting device for example is made of a polymer, the cutting device will start to release organic substances when the cutting device is degraded in a biological environment, such as a human body. This release may affect the function mechanisms of electrocardial signal transmission, since these function mechanisms are based on physiochemical diffusion effects causing change of pH, change of organic concentrations, and/or change of ionic concentrations, which physiochemical diffusion effects may be affected by the substances released by the cutting device when the cutting device is degraded.
  • Myocardial muscle cells presents activation potentials and charging conditions in respect of operation status .
  • cell membrane function may be affected by a change in pH, resulting from release of substances from the cutting device during degradation.
  • Change in organic concentrations may result in chelating effects in respect of ions, hydrophobic effects in the vicinity of the cell membrane, and/or pharmacological effects on cell membrane function, when substances are released from the cutting device during degradation.
  • Organic release even if the release is of carbondioxide and water, may influence membrane potential and function. This may for example be achieved by changing pH, changing the ion activity of specific ions needed for specific functions, such as Na or Ca. Release of oxalic acid anions may for example have a chelating effect on Ca.
  • ions may for example affect myocardial cell activity, such as through increase in Li and/or Mg concentrations causing short and/or long term changes in electrical signal transmission. According to an article of Fleed and Ferrans, it has been shown that especially Li, Mg, Ni, Co, and V may have these effects.
  • the release of substances from the cutting device itself may be combined, which combination affects myocardial signal propagation, may be used as a synergetic effect when treating atrial fibrillation.
  • the effect of the cutting device may therefore be enhanced by achieving a more immediate effect than only the cutting action.
  • a change in pH may result in an increase of local inflammation in myocardial muscle tissue.
  • Fast resorbing polymers such as poly (glycolic) acid, may have this effect on tissue.
  • more effective tissue reaction are known from the testing of resorbable copolymers, since they can degrade faster than their higher crystalline homopolymers from which they are made of. Examples of such copolymers are lactide/caprolactone copolymers . In one embodiment this effect is taken advantage of, since an increase in inflammation will result in larger area of scar tissue. A larger area of scar tissue will increase the effect of isolating signal transmition.
  • a polymer is designed as a resorbable polymer with the aim to release non-toxic and already known monomers by hydrolysis, such as glycolic acid or perhaps oxalic acid.
  • Resorbable classes of ceramics since they are build from metal oxides, may be designed to release ions causing the pH to change towards alkalic environment. Most resorbable ceramics are composed based on hydroxyapatite (Ca-phosphate salts) . Hydroxyapathite is from the chemical point of view a buffer which can be composed towards alkalic or acidic behaviour. It will also be possible, while being inside the scope of the present invention to to fill a resorbable system with anhydrides of acids or bases.
  • the cutting device may be manufactured of such polymers, with these advantages and possibilities.
  • the cutting device 26 may be designed such that it will be degraded or absorbed by the body after it has performed its change of shape.
  • a polylactic acid polymer and/or a polyglycolic acid polymer, poly ( ⁇ -caprolactone) or polydioxanone, according to above, 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 cutting device 26 may be tubular in both its temporary shape and its permanent shape, as shown in Figs 4-5.
  • the shape memory may be used for bringing the cutting device 26 between any shapes.
  • Some examples of shapes that are at least not entirely tubular are for example globular, spiral shaped, cork screw shaped, and shapes adapted to fit or be arranged in a specific area, such as in the heart. This specific area in the heart may be an atrium or a ventricle.
  • First picturing said tissue or area, and subsequently adapting the cutting device according to the obtained picture may for example perform the adaptation of the cutting device.
  • the shape of the cutting device 26 in its first state is preferably compact to facilitate insertion of the cutting device 26 through the vascular system.
  • a tubular shape is suitable, but other shapes, according to above, may be just as suitable.
  • the shape of the cutting device 26 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.
  • the shape of the cutting device 26 in its second state may be adjusted for fixing the cutting device 26 to its desired position within the body.
  • the cutting device 26 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 cutting device 26 will be facilitated.
  • the edges of the cutting device 26 facing the tissue to be penetrated may be made especially sharp to increase its effectiveness, as illustrated in Fig. 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.
  • drugs include 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 cutting device 26 with collagenase would particularly speed up the process of penetrating tissue.
  • the drugs are attached to the surface of the cutting device 26 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.
  • other methods may be used.
  • drugs preventing thrombosis and increasing in-growth of endothelium on the endothelial surface after penetration of the cutting device 26 may be attached to the cutting device 26.
  • Such drugs would be e.g. Endothelium Growth Factor, and Heparin.
  • other drugs designed to treat arrhythmias may be attached to the cutting device surface.
  • Such drugs are e.g. amiodarone and sotalol.
  • the cutting device according to the present invention is manufactured of a biodegradable material, it is also possible to integrate the drug, such as those mentioned above, in the biodegradable material.
  • the drug such as those mentioned above
  • the biodegradable material degrades in a biological environment, the drug is eluted continuously.
  • a drug, or a plurality of drugs may be integrated as sheets in the biodegradable material. This embodiment provides the possibility to elute a drug during separated time intervals, or elute different drugs at different points of time.
  • a drug, or a plurality of drugs are integrated homogenously in the biodegradable material.
  • a drug, or plurality of drugs integrated in the biodegradable material of the cutting device, and also coat the surface of the cutting device with a coating of a drug, or plurality of drugs.
  • This kind of coating may cover the whole cutting device or only a part of the cutting device, such as a cutting edge.
  • the cutting device comprising a drug, or a plurality of drugs
  • a biodegradable material not containing any drug or drugs.
  • one drug which is active on collagen or elastin
  • another drug may be included to act on muscle tissue.
  • the inside of the cutting device 26 inserted into a blood vessel will be in contact with the blood stream inside the blood vessel.
  • Such inside surface of the cutting device 26 may as well be covered with antithrombotic drugs.
  • drugs would be e.g. Heparin, Klopidogrel, Enoxaparin, Ticlopidin, Abciximab, and Tirofiban. It is also possible to integrate these drugs in the biodegradable material in the different ways described above.
  • Another way to increase the effectiveness of the cutting device 26 is to attach a metallic part of the cutting device 26 to electrical currency, which would provide a heating of the cutting device 26. Thereby, tissue may also be killed by this heating, enhancing the effect of the cutting device 26. Further, the force driving the change of shape will also be increased, speeding up the shape change of the cutting device.
  • tissue cutting devices may be chosen according to patient specific anatomy.
  • design parameters are for instance wire thickness distribution, connection points, fastening elements such as hooks, bistable sections or characteristics, material choice, implementation of drug delivery sections, timing design of cutting action, etc. as described in co-pending patent applications concurrently filed by same applicant as present application, which hereby are incorporated by reference herein in their entirety.
  • a method for treatment of disorders in the heart rhythm regulation system comprising inserting a tissue cutting device in a temporary delivery shape through the vascular system into a body vessel adjacent to the heart and/or into the heart; changing shape of the tissue cutting device, 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, thereby creating cutting action configured for cutting said heart tissue and/or said body vessel, thereby reducing undesired signal transmission in a heart tissue by isolating ectopic sites thereof by cutting said tissue by means of the tissue cutting device configured therefore, and biodegrading the tissue cutting device during or after said changing shape of the tissue cutting device from said expanded delivered shape to said further expanded shape .
  • 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.
  • 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 restraining comprises keeping the tissue cutting device inside a tube.
  • the restraining comprises cooling the tissue cutting device.
  • biodegrading the tissue cutting device comprises hydrolytically or enzymatically degradading said tissue cutting device.

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Abstract

L'invention concerne un dispositif servant au découpage de tissus, conçu pour être introduit par le système vasculaire dans un vaisseau corporel à proximité du coeur et/ou dans le coeur, puis pour être soumis à un changement de forme pour pénétrer dans le tissu cardiaque. Ce dispositif peut être utilisé pour traiter des troubles au niveau du système de régulation du rythme cardiaque. L'invention concerne également une trousse comprenant plusieurs dispositifs servant au découpage de tissus, permettant de produire une lésion précise pour le traitement de ce type de trouble. Le dispositif est conçu à partir d'un matériau biodégradable, tel qu'un matériau dégradable par voie hydrolytique ou un matériau dégradable par voie enzymatique.
EP06755236A 2005-05-17 2006-05-17 Dispositif biodegradable servant au decoupage de tissus, trousse et methode destines au traitement de troubles au niveau du systeme de regulation du rythme cardiaque Withdrawn EP1890637A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
EP06755236A EP1890637A1 (fr) 2005-05-17 2006-05-17 Dispositif biodegradable servant au decoupage de tissus, trousse et methode destines au traitement de troubles au niveau du systeme de regulation du rythme cardiaque

Applications Claiming Priority (3)

Application Number Priority Date Filing Date Title
PCT/EP2005/005363 WO2006122573A1 (fr) 2005-05-17 2005-05-17 Dispositif et necessaire pour le traitement des troubles du systeme de regularisation du rythme cardiaque
EP06755236A EP1890637A1 (fr) 2005-05-17 2006-05-17 Dispositif biodegradable servant au decoupage de tissus, trousse et methode destines au traitement de troubles au niveau du systeme de regulation du rythme cardiaque
PCT/EP2006/062400 WO2006122961A1 (fr) 2005-05-17 2006-05-17 Dispositif biodegradable servant au decoupage de tissus, trousse et methode destines au traitement de troubles au niveau du systeme de regulation du rythme cardiaque

Publications (1)

Publication Number Publication Date
EP1890637A1 true EP1890637A1 (fr) 2008-02-27

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EP06755236A Withdrawn EP1890637A1 (fr) 2005-05-17 2006-05-17 Dispositif biodegradable servant au decoupage de tissus, trousse et methode destines au traitement de troubles au niveau du systeme de regulation du rythme cardiaque

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Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20020058897A1 (en) * 1998-09-10 2002-05-16 Percardia, Inc. Designs for left ventricular conduit

Patent Citations (1)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20020058897A1 (en) * 1998-09-10 2002-05-16 Percardia, Inc. Designs for left ventricular conduit

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See also references of WO2006122961A1 *

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