SUMMARY OF THE INVENTION The present invention overcomes the drawbacks of previously-known LVAD systems and methods by providing an implantable pump system having an undulating membrane capable of producing a wide range of physiological flow rates while applying low shear forces to the blood, thereby reducing hemolysis and platelet activation relative to previously-known systems. Battery 40 preferably comprises a rechargeable battery capable of powering implantable pump 20 and controller 30 for a period of several days, e.g., 3-5 days, before needing to be recharged.
For example, programmer 50 may direct controller 30 to operate implantable pump 20 at a given frequency, amplitude and/or duty cycle during a period of time when a patient is typically sleeping and may direct controller 30 to operate implantable pump 20 at a different frequency, amplitude and or duty cycle during time periods when the patient is typically awake. It is expected that the patient will have available to him or her at least two batteries, so that while one battery is coupled to controller 30 to energize the controller and implantable pump, the other battery may be connected to a recharging station.
Dolor De Espalda
While a cardiac transplant may significantly prolong the patient’s life beyond the one year mortality rate, patients frequently expire while on a waitlist for months and sometimes years awaiting a suitable donor heart. Finally, the positive displacement pumps like the one described in the Isaacson patent are incapable of achieving pulsatility similar to that of the natural heart, e.g., roughly 60 to 100 beats per minute, while maintaining physiological pressure gradients. 21C-E, configurations are illustrated wherein controller 30 is directly electrically coupled to battery 40, such that controller 30 and battery 40 may be worn by the patient together, e.g., via a purse, shoulder bag, or holster. 21F-H, configurations are illustrated wherein controller 30 is remotely electrically coupled to battery 40, such that the weight and volume of controller 30 and battery 40 are distributed and may be worn by the patient separately, e.g., via a belt or a vest.
Fisioterapia Querétaro Calendarios
In these patents, vibratory motion applied to the deformable membrane causes wave-like undulations in the membrane that propel the fluid along a channel. 6 and 7 without departing from the invention described herein. In accordance with another aspect of the invention, controller 30 may be programmed by programmer 50 to operate at selected frequencies, amplitudes and duty cycles to achieve a wide range of physiologic flow rates and with physiologic pulsatilities. By adjusting the duty cycle, implantable pump 20 may be configured to generate a wide range of output flows at physiological pressure gradients. Moreover, the pump subjects the blood to significant pressure fluctuations as it passes through the pump, resulting in high shear forces and risk of hemolysis. In accordance with this function, an estimation of pump flow may be computed that does not require a flow sensor and which may be used to set the operating point of the pump.
- Dolores de espalda y cuello
- Temor y creencia de ser visto como ansioso, débil, raro, loco o estúpido
- Respuesta al tratamientu
- Para empezar, incorpora el jengibre molido en una taza de agua hirviendo
- Control remoto
For example, the average value of εk may be computed over an arbitrary number of samples. In accordance with one aspect of the invention, movements of magnetic ring assembly 76 may be translated to membrane assembly 82 which may be disposed concentrically below stator assembly 72. Membrane assembly 82 preferably is rigidly attached to magnetic ring assembly 76 by posts 81. In the embodiment depicted in FIG.
Dolores Musculares Remedios
The moving components are rigidly affixed to one another and do not incorporate any parts that would induce friction, such as mechanical bearings or gears. 1, in one embodiment, controller 30 and battery 40 are extracorporeal, and are sized so as to be placed on a belt or garment worn by the patient. Dolor muscular por nervios . Programmer 50 may be conventional laptop loaded with programmed software routines for configuring controller 30 and setting operational parameters that controller 30 uses to control operation of implantable pump 20. As discussed above, programmer 50 typically is located in a clinician’s office or hospital, and is coupled to controller 30 via cable 51 or wirelessly to initially set up controller 30, and then periodically thereafter as required to adjust the operational parameters as may be needed. 24A. For example, co-energy W may be approximated by a lookup table that stores the output co-energy W values of the FEM model simulation.
1|k is the predicted covariance matrix. In accordance with another aspect of the present invention, an alternative exemplary implantable blood pump system is provided. 1 depicts an exemplary embodiment of the pump system of the present invention comprising an implantable pump, controller, battery, programmer and mobile device. The design of such an energy efficient implantable pump that fulfils all the requirements mentioned above poses many challenges in terms of mechanical design and manufacturing process. In view of the foregoing, there exists a need for controlling an energy efficient implantable pump that has light weight, small size, and fast start and stop response, for example, without relying on position, velocity, or acceleration sensors. Due to the specific medium (blood) in which the pump is operating, it may be preferred to avoid adding position, velocity, or acceleration sensors that would significantly increase the complexity and size of a pump that is already difficult to design.
The controller is robust to pressure and flow changes inside the pump head, and allows fast change of pump’s operation point. Specially, implantable pump 20 may be sized and shaped to produce physiological flow rates ranging from 4 to 6 liters per minute at pressure gradients lower than a threshold value associated with hemolysis. The inlet cannula typically directly connected to the left ventricle, e.g., at the apex, and delivers blood from the left ventricle to the pump.
Dolores Musculares Por Ansiedad
Blood may enter implantable pump 20′ from the left ventricle through inlet cannula 21′ and flow downward along the pump assembly into delivery channel 100′. As the blood moves down tapered section 83′, it is directed through gap 74′ and into a vertical portion of delivery channel 100′ in the area between pump housing 27′ and actuator assembly 95′. As shown in FIG. Como quitarme el dolor de espalda . 6-9, blood may enter implantable pump 20 from the left ventricle through inlet cannula 21 and flow downward along pump assembly 70 into delivery channel 100, defined by the interior surface of pump housing 27 and exterior of pump assembly 70. Delivery channel 100 begins at the top of stator assembly 72 and extends between tapered section 83 and the interior of pump housing 27. As the blood moves down tapered section 83, it is directed through gap 74 and into a vertical portion of delivery channel 100 in the area between pump housing 27 and actuator assembly 95, and including in the gap between magnetic ring assembly 76 and electromagnet assembly 91. Delivery channel 100 extends down to flanged portion 87 of stator assembly 72, which routes blood into flow channel 101, within which membrane assembly 82 is suspended.