Method and device for detecting body haemodynamics response in in-vitro counterpulsation treatment

Abstract

The invention discloses a method and device for detecting body haemodynamics response in in-vitro counterpulsation treatment. The detection method comprises the steps that physiological information ofa sampler is acquired, and blood vessel and blood flow state data before and in in-vitro counterpulsation treatment are acquired respectively; an arterial tree is segmented based on an arterial treestructure model, blood segment length and radius data of a healthy volunteer are acquired, a baseline reference value is set, and an arterial tree geometric solution model is constructed; and boundaryconditions and correction and calibration conditions are calculated and set, flow and pressure pulse wave distribution of each position of the arterial tree is calculated on the basis of the pulse wave transmission theory and the model, and the blood perfusion and blood pressure levels of target blood vessel segments and visceral organs before and in the in-vitro counterpulsation treatment are calculated. The method and device can be used for noninvasive, real-time and effective analysis of the immediate haemodynamics effect of the in-vitro counterpulsation intervention treatment, and break the technical bottleneck of lack of an effective immediate haemodynamics effect evaluation method in the current in-vitro counterpulsation treatment.

Description

technical field [0001] The invention relates to the field of medical technology, in particular to a detection method and device for body hemodynamic response 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, brain a...

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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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