High efficiency external counterpulsation method

Abstract

The present invention provides a method for applying external counterpulsation to a patient, including detecting a blood-flow impedance signal, self-adaptive filter processing the detected blood-flow impedance signal, and adjusting inflation of an inflatable member based on the self-adaptive filter processing in order to optimize counterpulsation timing. A computer processes the signals and controls a fluid distribution device to distribute compressed fluid to a plurality of inflatable members based on said processed signals.

Description

CROSS-REFERENCE TO RELATED APPLICATIONS [0001] This application is a continuation of U.S. patent application Ser. No. 10 / 386,870 filed on Mar. 12, 2003, which is a continuation of U.S. patent application Ser. No. 09 / 435,583 filed on Nov. 8, 1999, now U.S. Pat. No. 6,572,621, which is a continuation of U.S. patent application Ser. No. 08 / 955,421 filed on Oct. 22, 1997, now U.S. Pat. No. 5,997,540, which is a continuation of U.S. patent application Ser. No. 08 / 711,129 filed on Sep. 9, 1996, now abandoned, which is a continuation of U.S. patent application Ser. No. 08 / 396,261 filed on Feb. 27, 1995, now U.S. Pat. No. 5,554,103, which is a continuation of U.S. patent application Ser. No. 08 / 058,394 filed on May 6, 1993, now abandoned. The disclosures of the above applications are incorporated herein by reference.FIELD OF THE INVENTION [0002] The present invention relates to an external counterpulsation apparatus and method for controlling the same, more particularly, to an improved effi...

AI Technical Summary

Problems solved by technology

However, this device is not only bulky and expensive, but it is also extremely noisy and complicated to operate.

It is, therefore, unsuitable for everyday clinical use.

However, this device is extremely bulky, noisy, and complicated to operate.

However, the deflation of the balloons of this apparatus lacks the suction of negative pressure and depends on natural exhaustion into the atmosphere.

Therefore, the exhaustion of the balloons is incomplete and slow, and leaves behind residual gas in the balloon which hinders the ability of this device to reduce afterload (workload) of the heart.

However, this apparatus is still ineffective in the exhaustion of all the pressurized gas in the balloons and in addition, it is still too large, noisy and heavy for transport to be of practical application in the clinical setting.

However, this device does not have negative suction to increase the rate of deflation of the balloons, and it is still extremely noisy and not very efficient in producing desirable counterpulsation hemodynamic effects, namely a high rate of inflation and effective deflation.

The foregoing external counterpulsation apparatuses have many advantages over the original one, but there are still many problems.

For example, the high pressure air produced by the air compressor has a high temperature when it arrives at the balloons, which may cause a feeling of discomfort or even pain for the patient; the balloon cuff used by the prior art external counterpulsation apparatus is made of soft materials such as leatherette, canvas and the like, which may have a high elasticity and extensibility, requiring the use of a large volume of gas to achieve the required pressure and resulting in the inability to quickly inflate the balloons for optimal rate of inflation.

Furthermore, dead space may be formed due to the misfit between the balloon cuff and the surrounded limb; the balloon cuff could slip downward during counterpulsing, thereby being incapable of efficiently driving blood from peripheral regions to the root of the aorta, which directly affects the effectiveness of the counterpulsation treatment.

All these factors reduce the efficiency of counterpulsation and require more pressurized gas to fill up dead space and more power from the compressor.

At the same time a reduction in the rate of inflation of the balloon results in hindering the effective compression of the body mass as well as vasculature.

However, earlobe pulse wave, finger pulse wave or temporal pulse wave are signals derived from microcirculation and may not reflect the true pulse wave from the great arteries such as the aorta.

Using the dicrotic notch as the true aortic valve closure is incorrect because the dicrotic notch is affected by many other factors such as the dampening effect of the vascular elasticity, reflective wave from tapering of the arteries and interference from previous pulse waves.

Furthermore, the various existing external counterpulsation apparatuses only measure the electrocardiograph signals of the patient to guard against arrhythmia.

Some of these variations may be advantageous, while some of them are potentially unsafe.

For patients with arteriosclerosis and phelbosclerosis, there is the danger of blood vessels breaking due to the increase in their internal pressure.

Furthermore, applying pressure to the limbs presses not only on the arteries but also the veins, and this may result in an increase in the amount of blood returning to the heart.

This may cause cardiac, lung or pulmonary edema because of the degration of the decrease in pumping capacity of the heart and incapability of the heart to pump out the increased amount of blood returning to the heart.

This may, in turn, affect the oxygen saturation in the arteries of the body and cause an oxygen debt.

Furthermore, the gas distribution device in the existing external counterpulsation apparatuses operate by controlling the opening and closing of the solenoid valves, which has the disadvantage of having voluminous and complex pipe connections.

This is disadvantageous to miniaturizing the whole apparatus and improving its portability.

Images