Classifications

• • A—HUMAN NECESSITIES
  • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
  • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
  • A61N2/00—Magnetotherapy
  • A61N2/06—Magnetotherapy using magnetic fields produced by permanent magnets

Definitions

• the present invention relates generally to cardiac treatment. More particularly, the present invention relates to a device for treatment of congestive heart failure.
• CHF Congestive heart failure
• systolic and/or diastolic left ventricular dysfunction is a condition associated with significant morbidity and mortality.
• Patients with CHF are typically identified upon presentation with dyspnea due to pulmonary edema and/or lower extremity swelling. Diagnostic criteria for CHF include history, physical examination, and chest radiographs.
• a 2010 update from the American Heart Association estimated that there were 5.8 million people with CHF in the United States in 2006. There are an estimated 23 million people with CHF worldwide. Additionally, the prevalence of heart failure increases rapidly with advancing age. In the Framingham Heart Study, the prevalence of heart failure in men was 0.8% at age 50-59 years, but increased to 6.6% by age 80-89 years. It has been estimated that the prevalence of heart failure is 25% higher in the African- American population than in the Caucasian population. Heart failure is the first-listed diagnosis in 875,000 hospitalizations and over 270,000 patients die from heart failure per year.
• Medical therapy for treatment of this disorder has improved significantly but remains limited after onset of the advanced stages of the disease.
• Medical therapies include diuretics, beta blockade, and angiotensin converting enzyme inhibitors. These agents improve symptoms and/or outcomes in many patients.
• diuretics beta blockade
• angiotensin converting enzyme inhibitors These agents improve symptoms and/or outcomes in many patients.
• treatment remains limited with diuretics, and vasodilator therapy if hemodynamically tolerated.
• inotropic agents are often utilized with modest improvement in contractility, but associated comorbidities including cardiac arrhythmia.
• Cardiac transplant can be an effective treatment, but the procedure is limited by organ shortages, procedural risks, and the lifelong requirement for immunosuppression.
• Mechanical support therapies including left ventricular assist devices such as the pulsatile-flow Heartmate XVE (HM1; Thoratec Corp., Pleasanton, CA, USA) or continuous -flow Heartmate II (HM2; Thoratec Corp.) can be used as a bridge to transplant or as destination therapy.
• left ventricular assist devices such as the pulsatile-flow Heartmate XVE (HM1; Thoratec Corp., Pleasanton, CA, USA) or continuous -flow Heartmate II (HM2; Thoratec Corp.) can be used as a bridge to transplant or as destination therapy.
• HM1 pulsatile-flow Heartmate XVE
• HM2 continuous -flow Heartmate II
• current technologies for mechanical cardiac support are limited by the invasive nature of their implantation (generally requiring open heart surgery), procedural risk, as well as long-term risks after implantation including infections and complications associated with extracorporeal and non-pulsatile flow such as thrombogenicity and gastrointestinal bleeding.
• ICD implantable cardioverter defibrillator
• biventricular pacemaker/ICD implantation for prevention of sudden death and/or for cardiac resynchronization in the setting of left bundle branch block. It is estimated that over 3 million patients in North America are eligible for an ICD, with over 400,000 additional patients meeting the criteria every year. While effective at preventing sudden death, ICDs do not prevent death from pump failure. Biventricular pacing can provide modest improvement in pump function in two thirds of recipients, but over a third of patients derive no symptomatic or survival benefit. [0007] It would therefore be advantageous to provide a treatment for congestive heart failure that is less invasive and minimizes patient risks, such as infection and thrombogenicity.
• a device for providing magnetic assistance to a chamber of a heart includes a first magnet positioned adjacent to a first wall of the chamber of the heart and a second magnet positioned adjacent to a second wall of the chamber of the heart.
• An electrode is configured to sense electrical output in the heart.
• the electrode is positioned within the chamber of the heart.
• a generator is coupled to the first magnet, the second magnet, and the electrode, and the generator is in conductive communication with the first magnet, the second magnet, and the electrode.
• the first magnet and the second magnet are configured to attract during systole and repel during diastole.
• the generator includes a battery.
• the generator can further include an external drive to provide power.
• Electrical leads can be used to connect the generator to the first and second magnet and the electrode.
• the first magnet can take the form of a static magnet and said second magnet can take the form of an electromagnet.
• the electrode can take the form of an electrode pair configured to sense a QRS wave produced by the heart, and further can be configured to produce a bipolar electrogram.
• the first magnet and the second magnet can be positioned on outer surfaces of opposing walls of the chamber of the heart. More particularly, the first magnet can be positioned on an endocardium of a right ventricle of the heart, and the second magnet can be positioned in a lateral branch of a coronary sinus.
• a method for providing magnetic assistance to a chamber of a heart includes positioning a first magnet adjacent to a first wall of the chamber of the heart and positioning a second magnet adjacent to a second wall of the chamber of the heart.
• the method includes positioning an electrode within the chamber of the heart.
• the electrode is configured to sense electrical waves within the heart.
• the method includes coupling a generator to the first magnet, the second magnet, and the electrode.
• the generator is in conductive communication with the first magnet, the second magnet and the electrode.
• the method also includes configuring the first magnet and the second magnet to attract during systole and repel during diastole in synchrony with a QRS wave of the heart.
• FIG. 1 illustrates a schematic view of a magnetic assist device for a left ventricle of a heart, according to an embodiment of the present invention.
• FIG. 2 illustrates a graphical view of the force between two groups of four permanent magnets in each group, as a function of distance.
• FIG. 3 illustrates an image of a prototype electromagnet (left) and an image of a static magnet (right), according to an embodiment of the present invention.
• FIG. 4 illustrates an X-ray view of the magnets of FIG. 3, revealing coils embedded within plastic in the electromagnet (left) and 4 static magnets (right), according to an embodiment of the present invention.
• An embodiment in accordance with the present invention provides a magnetic assist device to treat congestive heart failure.
• the device includes at least two magnets implanted on the heart and synchronized to the QRS wave, as sensed by an electrode disposed within the heart.
• one of the magnets is disposed on the endocardium of the right ventricle and the other magnet is positioned in a lateral branch of the coronary sinus.
• the two magnets are attracted to one another to aid in contraction of the heart muscle.
• the two magnets repel one another to aid in relaxation of the heart muscle.
• a generator disposed trans dermally, is conductively connected to the two magnets and the electrode, such that the generator powers the magnets and the electrode.
• the generator can be powered by an internal battery and/or external drive.
• the device described herein has the capacity to aid the systolic and diastolic function of a cardiac chamber using magnetic fields applying ECG synchronized attraction (systolic) and repulsion (diastolic) forces on the outside of cardiac chambers.
• the device can be implanted using techniques similar to biventricular
• pacemaker/ICD implantation and may ultimately combine, in one device, the benefits of magnetic assist, pacing, and defibrillation.
• FIG. 1 illustrates a schematic diagram of a magnetic assist device for a left ventricle of a heart, according to an embodiment of the present invention.
• the device 10 includes a first magnet 12 and a second magnet 14 disposed within a heart 16 of the patient.
• the device 10 also includes an electrode 18 disposed within the heart 16.
• a generator 20 is disposed transdermally, and is conductively coupled to the first and second magnets 12, 14 and the electrode 18, via leads 22.
• the leads 22 can take the form of a single branched lead or can take the form of multiple leads connected to the first and second magnets 12, 14 and the electrode 18.
• FIG. 1 illustrates the device 10 configured for left ventricular assist. While this is included as an example, it is not meant to be considered limiting, and such a device can be used to assist any chamber or region of the heart, as is known to or conceivable by one of skill in the art.
• the first and second magnets 12, 14 are disposed on outer walls of the left ventricle 24. More specifically, the first magnet 12 is disposed in the right ventricle 26, such that it is on a first outer wall 28 of the left ventricle 24.
• the second magnet 14 is disposed in a lateral branch of the coronary sinus 30, such that it is on a second outer wall 32 of the left ventricle 24.
• the electrode is also disposed within the right ventricle 26, in order to sense the QRS for the left ventricle.
• the leads 22 extend from the generator 20 to the first and second magnets 12, 14 and to the electrode 16, through the atria, in a manner similar to a standard lead for pacing or defibrillation.
• the magnets 12, 14 are configured to attract each other during systole and repel each other during diastole, thus augmenting cardiac work both during contraction and relaxation.
• the magnets 12, 14 and electrode 16 can be implanted surgically or alternately threaded through the vasculature. More particularly, a subclavian approach can be used for placement of the right ventricular lead, and coronary sinus epicardial lead.
• the device components can also be implanted in any other suitable fashion known to one of skill in the art.
• the first magnet 12 can take the form of a static magnet. Alternately, the first magnet 12 can take the form of any suitable magnet, known to or conceivable by one of skill in the art.
• the second magnet 14 can take the form of a standard electromagnet or any other suitable magnet known to or conceivable by one of skill in the art. While the first and second magnets 12 and 14 are discussed as singular magnets, they can also take the form of a group of magnets having a number deemed suitable by one of skill in the art.
• the electrode 16, can take the form of a pair of electrodes configured to detect QRS wave in the ventricles or P wave in the atria.
• the first and second magnets 12, 14 can then be synchronized to attract during systole and repel during diastole.
• one or both of the first and second magnets has to take the form of an electromagnet, in conductive communication with the generator 20.
• the first and second magnets 12, 14 augment cardiac work during contraction and relaxation.
• the electrode 16 can be configured to output a bipolar electrogram.
• the generator 20, illustrated in FIG. 1, can include a battery to provide the power necessary to polarize the magnets or can include a driveline for an external battery pack to provide additional power.
• a driveline is commonly used in conventional cardiac assist devices and is known to those skilled in the art.
• the voltage needed to power the generator 20 is likely greater than that needed for a standard pacemaker or defibrillator. It is also possible that the device as described above could be used to supplement the right ventricle in a case of right ventricular failure, for diffuse atriopathy, or even restoration of the atrial kick in the setting of atrial fibrillation.
• the magnets can take the form of traditional magnets or electromagnets.
• Ka magnetostatic energy constant defined as K d ⁇ ⁇ ⁇ ⁇ ⁇ 12 ( ⁇ o is permeability of vacuum which is 1.2566371 x 10-6 H/m, and M is the saturation magnetization of the magnets in MA/m).
• 3 ⁇ 4 5 MJ/m 3 .
• R is the radius of each of the magnets, x is the distance between their centers and t is the thickness of the magnets (in meters).
• the force between two groups of permanent magnets is calculated as a function of the distance between them.
• Each of the magnets is, for the purposes of the example, assumed to be 5 mm in diameter and 1 mm thick. Thus a patch of 4 magnets would occupy 4 cm 2 of an over 150 cm 2 of epicardial surface. It is apparent that larger contribution would be offered as the contraction proceeds.
• Electromagnets are coils that develop a magnetic field when an electrical current is passed.
• Mumetal cores have high relative permeability (20,000) and can increase the magnetic field created by the solenoid substantially.
• a single coil of similar dimensions as one of the permanent magnets analyzed above can generate 0.1 Tesla flux with a 2000 turn solenoid and a 1 A current. This field strength would be comparable to that estimated from the small magnet model in the previous paragraph.
• FIG. 2 illustrates a force between two groups of four permanent magnets each (5mm diameter and 1mm thickness) as a function of the distance.
• the magnets are most effective at the apex where open chest cardiac massage has been shown to be most effective. Near the apex, even is dilated hearts, the magnet distance is typically less than 3 cm. Additionally, the magnets can be implanted in a hinge configuration which maximizes the generated force due to the proximity of the more apical magnets. The forces (exceeding 1 lb) calculated by this conservative estimate would augment a failing heart in great excess of the added force by using intravenous inotropic agents. In contrast to the proposed device, effective intravenous inotropy is arrhythmogenic and patients develop rapid tachyphylaxis. Importantly, to be clinically beneficial, generation of enough force for complete left ventricular contraction or relaxation is not necessary. Current clinically utilized devices and agents that result in mild augmentation of the contraction or relaxation process often improve symptoms significantly.
• FIGS. 3 and 4 illustrate exemplary implantable magnets, according to an embodiment of the present invention.
• these exemplary magnets are not to be considered limiting, and it is expected that the electromagnets can be miniaturized to enable future versions for minimally invasive implantation.
• the magnets are embedded in a soft, biocompatible plastic material that allows the magnets to be sutured to the cardiac muscle of the heart and more particularly to the epicardial surface.
• the magnets need not be embedded in the plastic, and the embodiment illustrated in FIGS. 3 and 4 is simply an example of a device according to the present invention that is capable of being sutured to the epicardial surface.
• FIG. 3 illustrates an image of electromagnet (left) and a group of static magnet (right), and FIG. 4 illustrates an X-ray of the electromagnet (left) and the group of 4 static magnets right, also illustrated in FIG. 3.
• the magnets cannot be utilized for the first few months. It typically takes 3 months before fibrotic tissue envelopes develop around the device leads, thus fully securing the components to the cardiac muscle. Activation of the magnets prior to fibrosis and endothelialization may lead to dislodgement. However, based upon lead extraction experience, after the first 3 months, the device will be secure enough to withstand the generated forces without dislodgement. Such a time limitation would not apply to endoscopic approaches for device placement by electrophysiologists or device placement by cardiac surgeons.
• An additional element of the present invention is the power requirement for the device, which will likely require a driveline for continuous use.
• incorporation of inductive charging by utilization of an electromagnetic field to transfer energy to the subcutaneous generator can obviate the need for a driveline.
• an induction coil would be utilized to create an alternating electromagnetic field from within a charging base station, and a second induction coil in the implanted generator to receive power from the electromagnetic field and convert it back into electrical current to charge the battery.
• Any other suitable means of powering the device known to or conceivable by one of skill in the art could also be used.

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Citations (5)

• 2013
  • 2013-07-01 WO PCT/US2013/048859 patent/WO2014005135A1/fr not_active Ceased

Patent Citations (5)

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