Method and device for detecting body hemodynamic response in external counterpulsation therapy

Abstract

The invention discloses a method and a device for detecting the body's hemodynamic response in external counterpulsation therapy. The detection method includes: collecting physiological information of a sampler, and performing blood vessel and blood flow state data before and during external counterpulsation therapy. Acquisition; segment the arterial tree based on the arterial tree structure model, collect the length and radius data of each blood vessel segment of healthy volunteers, set the baseline reference value, and construct the geometric solution model of the arterial tree; calculate and set the boundary conditions, correction and calibration conditions, and Based on the pulse wave transmission theory and model, the flow rate and pressure pulse wave distribution at each position of the arterial tree are solved and calculated, and the blood perfusion and blood pressure levels of target blood vessel segments and organs before and during external counterpulsation treatment are calculated. The invention can non-invasively, real-time and effectively analyze the immediate hemodynamic effect of external counterpulsation intervention treatment, and solves the technical bottleneck that the current external counterpulsation therapy lacks an effective instant hemodynamic effect evaluation method.

Description

technical field [0001] The invention relates to the field of medical technology, in particular to a method and device for detecting hemodynamic response of a body in external counterpulsation therapy. Background technique [0002] The working principle of external counterpulsation therapy is: wrap a special airbag cover on the patient's calf and buttocks, detect the R wave of the patient's electrocardiogram by the electronic control device, and calculate the systolic and diastolic periods of the heart in real time through the computer. Instruct the air source device to inflate and deflate each section of airbags. During the diastolic period, each section of airbags is inflated sequentially from far to near with a time difference of about 50ms to increase diastolic pressure, drive arterial blood back to the upper body, and increase venous pressure. Return the blood volume to the heart, improve the blood perfusion of the important organs of the upper body such as the heart, br...

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Problems solved by technology

[0004] However, the pulse wave of the heart, brain, lower limbs, etc. is different from the finger pulse wave, especially when there are lesions and plaques in the circulatory system

Therefore, the current method of simply using the D / S value of the volume wave waveform of the finger pulse as the immediate effect evaluation standard of external counterpulsation therapy is inaccurate and has huge defects. This is also the reason why patients with different diseases and individual differences receive external feedback One of the root causes of the often large differences in curative effect after stroke therapy

[0005] In addition, the current interventional measurement technology is not suitable for external counterpulsation therapy due to its invasiveness, and the non-interventional measurement technology can only obtain the blood flow velocity of some superficial blood vessels

Neither intervention nor non-intervention can effectively evaluate the overall hemodynamic response of the body in external counterpulsation intervention, especially the hemodynamic status of important parts such as coronary artery and aorta

The rapid development of hemodynamic numerical simulation technology in recent years, especially the one-dimensional model based on the pulse wave transfer theory, provides a new idea for effectively evaluating the hemodynamic characteristics of the body. However, the current one-dimensional model still has limitations. It is extremely time-consuming and expensive. At the same time, the pulse wave transfer model uses the aortic valve outlet and the blood flow wave at the ascending aorta as the only inlet boundary conditions. However, due to the closure of the aortic valve during diastole, the one-dimensional model cannot reflect The intervention of external counterpulsation on diastolic waves requires a substantial improvement of the model itself

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