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  Sensor-equipped and algorithm controlled direct mechanical ventricular assist deviceUSPTO Application #: 20060142634Title: Sensor-equipped and algorithm controlled direct mechanical ventricular assist device Abstract: An apparatus for assisting the function of a heart disposed within a body. The apparatus can apply a compressive force and an expansive force to a portion of the outer wall of the heart. The apparatus can comprise a cup-shaped shell having an exterior wall, an interior wall, an apex, and an upper edge; a liner having an outer surface and an inner surface, an upper edge joined to the interior wall of the cup-shaped shell, and a lower edge joined to the interior wall of the cup-shaped shell, thereby forming a cavity between the outer surface thereof and the interior wall of the shell; and a drive fluid within the cavity. The drive fluid can apply a force on a portion of the outer wall of the heart. (end of abstract) Agent: Buchanan Ingersoll PC (including Burns, Doane, Swecker & Mathis) - Alexandria, VA, US Inventors: Mark P. Anstadt, George L. Anstadt, Stuart G. MacDonald, Jeffrey L. Helfer, George W. Anstadt USPTO Applicaton #: 20060142634 - Class: 600016000 (USPTO) Related Patent Categories: Surgery, Cardiac Augmentation (pulsators, Etc.) The Patent Description & Claims data below is from USPTO Patent Application 20060142634. Brief Patent Description - Full Patent Description - Patent Application Claims
CROSS-REFERENCE TO RELATED APPLICATIONS [0001] This application is a divisional of Ser. No. 10/607,434, filed on Jun. 26, 2003. [0002] This invention relates in one embodiment to devices that assist a weak heart in providing the required pumping of blood, and more particularly to a mechanical cardiac assistance device which envelops the heart and applies periodic and focused hydraulic pressure waves to the heart in order to drive ventricular action (compression and expansion) in the proper sequence and intensity. FIELD OF THE INVENTION [0003] Mechanical devices that assist the human heart by providing proper systolic and diastolic actuation and circulatory function. BACKGROUND OF THE INVENTION [0004] Traditional medical and surgical treatment of patients with failing pump function of the heart is limited to blood-contacting devices which are technically difficult to install and result in complications related to such blood contact as well as technical aspects of device installation. Inadequate cardiac output remains a cause of millions of deaths annually in the United States. Mechanical devices are proving to be a practical therapy for some forms of sub-acute and chronic low cardiac output. However, all currently available devices require too much time to implant to be of value in acute resuscitation situations, resulting in loss of life before adequate circulatory support can be provided. Furthermore, other non-blood contacting devices similar to the current invention provide inadequate augmentation of cardiac function. Mechanical cardiac assistance devices generally operate by providing blood pumping support to the circulation to assist the failing heart. [0005] A number of mechanical techniques for assisting heart function by compressing its outer epicardial surface have been described and studied. These methods have focused on improving cardiac performance by assisting the systolic (positive pumping) function of the heart. Such techniques have been described as "direct cardiac compression" (DCC). DCC methods have been investigated only in the laboratory setting, and there are no uses of such devices in human subjects known to the applicants. Investigations regarding DCC have focused primarily on left ventricular (LV) systolic and diastolic performance. [0006] Examples of DCC techniques include, but are not limited to, cardiomyoplasty (the technique of wrapping skeletal muscle around the heart and artificially stimulating it), the Cardio support system (Cardio Technologies, Inc., Pinebrook, N.J.) and the "Heart Booster" (Abiomed, Inc., Danvers, Mass.). Cumulative results from laboratory investigations using these devices have all resulted in similar findings. Specifically, DCC has been shown to enhance left ventricular (LV) pump function without any apparent change in native LV oxygen consumption requirements; thereby, DCC has been shown to improve LV pump function without increasing myocardial oxygen consumption and/or requiring extra work from the heart. [0007] DCC devices have been shown to only benefit hearts with substantial degrees of LV failure. Specifically, DCC techniques only substantially improve the systolic function of hearts in moderate to severe heart failure. In addition, the benefits of DCC techniques are greater when applied to the relatively dilated or enlarged LV. Therefore the relative degree of assistance provided by DCC improves as heart failure worsens and the heart enlarges or dilates from such failure. DCC techniques clearly have a negative effect on diastolic function (both RV and LV diastolic function). This is exhibited by reductions in diastolic volume that, in part, explains DCC's inability to effectively augment the heart without at least moderate degrees of failure. This also explains DCC's efficacy being limited to sufficient degrees of LV size and/or dilatation, with significant dependence on preload, and/or ventricular filling pressures. Thus, DCC requires an "adequate" degree of heart disease and/or heart failure to benefit the heart's function. In addition, DCC devices have negative effects on the dynamics of diastolic relaxation and, in effect, reduce the rate of diastolic pressure decay (negative dP/dt max), increasing the time required for ventricular relaxation. This better explains why DCC techniques require substantial degrees of LV and RV loading (i.e. increased left and right atrial pressure or "preload") to be effective, as such increases serve to augment ventricular filling. This latter point is particularly true with smaller heart size and/or less ventricular distension. [0008] The critical drawbacks to DCC methods are multi-factorial and are, in part, summarized in the following discussion. First, and foremost, these techniques do not provide any means to augment diastolic function of the heart necessary to overcome their inherent drawback of "effectively" increasing ventricular stiffness. This is illustrated by the leftward shifts in the end-diastolic pressure-volume relationship (EDPVR) during DCC application. This effect on the EDPVR is seen with DCC devices in either the assist or non-assist mode. Clearly, RV diastolic function is impaired to a far greater degree by DCC due to the nature both the RV wall and intra-cavity pressures. Furthermore, studies of DCC devices have all overlooked the relevant and dependent impact these techniques have on right ventricular dynamics, septal motion and overall cardiac function. Because the right ventricle is responsible for providing the "priming" blood flow to the left ventricle, compromising right ventricular function has a necessary secondary and negative impact on left ventricular pumping function when these load-dependent devices are utilized. Furthermore, the ventricular septum lies between the right and left ventricle and is directly affected by the relevant forces placed on both the RV and LV. Another related and fundamental drawback to DCC devices is their inability to continuously monitor ventricular wall motion and chamber dynamics that are intuitively critical to optimizing the assist provided by such mechanical actions on the right and left ventricular chambers which behave in an complex, inter-related fashion. Finally, studies regarding DCC methods have failed to adequately examine the effects of these devices on myocardial integrity. [0009] The Direct Mechanical Ventricular Assist device (hereinafter abbreviated as DMVA) is an example of one type of mechanical cardiac assistance device. In general, a DMVA system comprises two primary elements: (a) a Cup having dynamic characteristics and material construction that keep the device's actuating liner membrane or diaphragm closely conformed to the exterior surface (or epicardium) of the heart throughout systolic and diastolic actuation, and (b) a Drive system and control system combination that cyclically applies hydraulic pressure to a compression and expansion liner membrane or membranes located on the interior surfaces of the Cup in a manner that augments the normal pressure and volume variations of the heart during systolic and diastolic actuation. The cyclic action of the device cyclically pushes and pulls on the left and right ventricles of the heart. [0010] By providing this cyclic motion at the appropriate frequency and amplitude, the weakened, failing, fibrillating, or asystolic heart is driven to pump blood in a manner which approximates blood flow generated by a normally functioning heart. Pushing inwardly on the exterior walls of the heart compresses the left and right ventricles into systolic configuration(s), thereby improving pump function. As a result, blood is expelled from the ventricles into the circulation. Immediately following each systolic actuation, the second phase of the cycle applies negative pressure to the liner membrane to return the ventricular chambers to a diastolic configuration by pulling on the outer walls of the heart. This is termed diastolic actuation and allows the ventricular chambers to refill with blood for the next compression. [0011] In the preferred embodiment of the present invention, the Cup is installed on the heart typically by using apical vacuum assistance, i.e. vacuum applied to the apex of the Cup. Such a preferred embodiment enables a non-traumatic and technically simple means of cardiac attachment of the Cup device in the patient and facilitates diastolic actuation. To install the Cup, the heart is exposed by a chest incision. The Cup is positioned over the apex of the heart in a position such that the apex of the heart is partially inserted therein. A vacuum is applied to the apex of the Cup, thereby pulling the heart and the Cup together, such that the apices of the Cup and the heart, and the inner wall of the Cup and the epicardial surface of the heart become substantially attached. Connections are then completed for any additional sensing or operational devices (typically integrated into a single interface cable) if the particular Cup embodiment comprises such devices. This procedure can be accomplished in minutes, and it is easy to teach to individuals with minimal surgical expertise. [0012] Effective DMVA requires that the Cup and Drive system satisfy multiple and complex performance requirements. Preferred embodiments of the Cup of the present invention satisfy these critical performance requirements in a manner that is superior to prior art DMVA devices. [0013] Heretofore, a number of patents and publications have disclosed Direct Mechanical Ventricular Assist devices and other cardiac assistance devices, the relevant portions of which may be briefly summarized as follows: [0014] U.S. Pat. No. 2,826,193 to Vineberg discloses a Ventricular Assist device that is held to the heart by a flexible draw-string. Vineberg uses a mechanical pump to supply systolic pressure to the heart to assist the heart's pumping action. [0015] U.S. Pat. No. 3,034,501 to Hewson discloses a similar Ventricular Assist device, comprised of silastic, which permits varying pressures to be exerted on various portions of the heart. [0016] U.S. Pat. No. 3,053,249 to Smith discloses a Ventricular Assist device capable of delivering systolic pressure to a heart. The Smith device utilizes adhesive straps to attach the device to the heart. [0017] U.S. Pat. No. 3,233,607 to Bolie illustrates a Direct Assist device that varies the level of systolic pressure depending on the changes of blood flow occasioned by exercise. The Bolie device claims to be fully implantable. U.S. Pat. No. 3,449,767 to Bolie discloses a system for controlling the pressure delivered to the balloons that control the DMVA unit. [0018] U.S. Pat. No. 3,279,464 to Kline teaches a method of manufacture of a Ventricular Assist device. Kline's device provides only systolic pressure to the heart. [0019] U.S. Pat. No. 3,371,662 to Heid discloses a Ventricular Assist device in the form of a cuff. The cuff may be implanted with defibrillating electrodes. [0020] U.S. Pat. No. 3,376,863 to Kolobow illustrates a Ventricular Assist device that delivers systolic pressure to the heart. The Kolobow device possesses an expandable collar about the periphery of the device's opening. The heart may be sealed within the device by expanding the collar. [0021] U.S. Pat. No. 3,455,298 of Anstadt discloses a Direct Mechanical Ventricular Assist device capable of delivering both systolic and diastolic pressures. The diastolic action is achieved by use of a vacuum. A second vacuum source functions to hold the device to the heart. Anstadt further defines the geometry of the device in U.S. Pat. No. 5,119,804. The geometry of the invention is described so as to accommodate hearts of various sizes as well as prevent the heart from being expelled from the device during the systolic expansion of the bladders. 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