WO2019114034A1 - 一种根据超声弹性肌动图获取生物力学参数的方法及装置 - Google Patents

一种根据超声弹性肌动图获取生物力学参数的方法及装置 Download PDF

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WO2019114034A1
WO2019114034A1 PCT/CN2017/118725 CN2017118725W WO2019114034A1 WO 2019114034 A1 WO2019114034 A1 WO 2019114034A1 CN 2017118725 W CN2017118725 W CN 2017118725W WO 2019114034 A1 WO2019114034 A1 WO 2019114034A1
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muscle
dynamic
elastic
skeletal muscle
image
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French (fr)
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肖扬
郑海荣
王丛知
牛丽丽
邓志婷
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Shenzhen Institute of Advanced Technology of CAS
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Shenzhen Institute of Advanced Technology of CAS
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Priority to EP17934679.6A priority patent/EP3566655B1/en
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/08—Clinical applications
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/48—Diagnostic techniques
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/48—Diagnostic techniques
    • A61B8/485—Diagnostic techniques involving measuring strain or elastic properties
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/5207—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of raw data to produce diagnostic data, e.g. for generating an image
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/5215—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/52—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves
    • A61B8/5215—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data
    • A61B8/5223—Devices using data or image processing specially adapted for diagnosis using ultrasonic, sonic or infrasonic waves involving processing of medical diagnostic data for extracting a diagnostic or physiological parameter from medical diagnostic data

Definitions

  • the present application relates to the field of testing technology, and in particular, to a method and apparatus for acquiring biomechanical parameters according to an ultrasound elastic muscle map.
  • Muscle is an important tissue that constitutes the human body, accounting for 40% to 45% of body weight. It is divided into three types: skeletal muscle, smooth muscle and myocardium. It is distributed around various organs and bones and has different structural, mechanical properties and functions. The musculoskeletal system relies on the binding force of the muscles to maintain stability, and relies on the driving force of the muscles to form a behavioral movement, which plays a vital role in human movement.
  • the testing of muscle biomechanical parameters is mainly based on ultrasonic shear wave elastography.
  • the ultrasonic shear wave elastography technology achieves a real quantitative measurement of muscle tissue elasticity.
  • the basic principle is: ultrasonic transduction
  • the radiation generated by the device generates a shear wave near the focus position, and then measures the propagation velocity of the shear wave in the tissue to calculate the elastic modulus of the tissue.
  • the muscle biomechanical parameters are mainly measured based on the ultrasonic shear wave elastography technique in the following manner: (1) Measuring the elastic modulus value of the skeletal muscle in a relaxed state, by a single elastic modulus value difference Assess that muscle is the source of power for the body to complete various movements. During the exercise, the muscle force will cause the elastic modulus to change. The elastic modulus value under the muscle relaxation state intelligently reflects the hardness when the muscle strength is zero, which cannot fully characterize its biomechanics. characteristic. (2) The elastic modulus values of the skeletal muscles under the relaxed state and the tension state (active contraction) were separately measured to evaluate the function and tension of the muscles, but the active contraction produced muscle strength was difficult to make a quantitative assessment. (3) Measure the elastic modulus values of skeletal muscles at different joint angles, and study the biomechanical properties of muscle rent under tensile state, but different joint angles are still qualitative index parameters, which vary from person to person and cannot be on muscle strength. Make a quantitative assessment.
  • the existing method based on ultrasonic shear wave elastography to test muscle biomechanical parameters can not obtain dynamic information, and can not be quantitatively obtained, so the obtained muscle biomechanical parameters are not accurate.
  • the purpose of the present application is to provide a method and apparatus for testing muscle biomechanical parameters, obtaining dynamic biomechanical parameters and improving the accuracy of obtaining muscle biomechanical parameters.
  • the present application provides a method for obtaining biomechanical parameters based on an ultrasound elastic myogram, comprising:
  • the ultrasonic elastic modulus curve is generated with the synchronous elastic modulus value as the ordinate, and the muscle biomechanical parameters are estimated according to the ultrasonic elastic muscle motion curve.
  • an embodiment of the present application provides a first possible implementation of the first aspect, the muscle dynamics image comprising a displacement image, the muscle dynamics parameter comprising a muscle stretch length, in the synchronous acquisition Before the dynamic muscle dynamics image sequence and the dynamic elastic image sequence in the continuous stretching of the single skeletal muscle, the method further comprises:
  • the distance from the feature point to the opposite end of the muscle tissue elongation end of the monolithic skeletal muscle is calculated to obtain an initial length of the skeletal muscle.
  • determining characteristic points of the muscle tissue elongation end of the monolithic skeletal muscle comprises:
  • the control ultrasonic diagnostic apparatus scans the longitudinal section of the single skeletal muscle along the direction of the muscle bundle by an imaging mode, and uses the detected joint point of the single skeletal muscle and the tendon as the feature point.
  • the implementation of the present application provides a third possible implementation of the first aspect, the acquiring the dynamic muscle power
  • the muscle dynamics parameters corresponding to each muscle dynamic image in the image sequence include:
  • the sum of the initial length and the effective value of the displacement change is recorded as the muscle stretch length corresponding to the displacement image.
  • the implementation of the present application provides a fourth possible implementation manner of the first aspect, the acquiring a feature point of the feature point in a relative initial state in the displacement image
  • the effective values of the displacement change of the position include:
  • the displacement change of the feature point position in the displacement image relative to the initial state is taken as the effective value.
  • the present application provides a fifth possible implementation of the first aspect, prior to the simultaneous acquisition of a dynamic muscle dynamic image sequence and a dynamic elastic image sequence during continuous stretching of a single skeletal muscle.
  • the method also includes:
  • the muscle abdomen position of the monolithic skeletal muscle is determined to acquire the dynamic elastic image sequence at the muscle belly position.
  • the present application provides a sixth possible implementation of the first aspect, the determining the abdominal position of the monolithic skeletal muscle, comprising:
  • the control ultrasonic diagnostic apparatus scans a transverse section of the skeletal muscle perpendicular to the direction of the muscle bundle by an imaging mode, and positions the largest cross section as the muscle abdomen position of the single skeletal muscle.
  • the implementation of the present application provides a seventh possible implementation manner of the first aspect, where the dynamic dynamic image sequence is obtained
  • the elastic modulus values corresponding to the dynamic elastic images include:
  • the present application is implemented
  • An eighth possible embodiment of the first aspect is provided, after the ultrasonic elastic muscle map is generated by using the muscle dynamics parameter as the abscissa and the synchronized elastic modulus value as the ordinate.
  • the method further includes:
  • the embodiment of the present application provides a ninth possible implementation of the first aspect, the muscle dynamics image comprising a displacement image, the muscle dynamics parameter comprising muscle stretching Length, the estimating muscle biomechanical parameters according to the ultrasound elastic muscle map curve includes:
  • the ductility is the difference between the maximum stretched length of the monolithic skeletal muscle and the length of the monolithic skeletal muscle in a relaxed state;
  • the model formula is determined according to a Gauss-Newton iteration method to determine the hardness index of the single skeletal muscle.
  • an apparatus for acquiring muscle biomechanical parameters according to an ultrasound elastic muscle map including:
  • An acquisition module for synchronously acquiring dynamic muscle dynamic image sequences and dynamic elastic image sequences during continuous stretching of a single skeletal muscle
  • an acquiring module configured to respectively acquire a muscle dynamic parameter corresponding to each muscle dynamic image in the dynamic muscle dynamic image sequence, and an elastic modulus value corresponding to each elastic image in the dynamic elastic image sequence;
  • a determining module configured to generate an ultrasound elastic muscle motion curve with the muscle dynamics parameter as an abscissa, and the synchronized elastic modulus value as an ordinate, and estimate muscle biomechanical parameters according to the ultrasonic elastic muscle motion curve .
  • the embodiment of the present application acquires the dynamic muscle dynamic image sequence and the dynamic elastic image sequence when the single skeletal muscle is continuously stretched, and respectively obtains the corresponding muscle dynamic image in the muscle dynamic image sequence.
  • the muscle map curve is used to estimate the muscle biomechanical parameters according to the ultrasonic elastic muscle map curve. It can be seen that the muscle dynamic parameters and the elastic modulus values obtained in the present application are the measured parameters measured during continuous stretching of the single skeletal muscle. And finally the ultrasound elastic muscle map curve, from which the biomechanical parameters of the single skeletal muscle during continuous stretching can be estimated, and the biomechanical parameters thus obtained are dynamic and quantitative.
  • FIG. 1 is a flow chart showing a method for obtaining muscle biomechanical parameters according to an ultrasound elastic myocardogram provided by an embodiment of the present application
  • FIG. 2 is a flow chart of a method for obtaining an initial length of skeletal muscle provided by an embodiment of the present application
  • FIG. 3 is a sequence diagram of a displacement image provided by an embodiment of the present application.
  • FIG. 4 is a sequence diagram of an elastic modulus provided by an embodiment of the present application.
  • FIG. 5 is a flow chart showing a method for obtaining skeletal muscle muscle stretching length according to an embodiment of the present application
  • FIG. 6 is a flow chart showing the elastic modulus values corresponding to the dynamic elastic images provided by the embodiments of the present application.
  • FIG. 7 is a flow chart showing a method for estimating muscle biomechanical parameters provided by an embodiment of the present application.
  • FIG. 8 is a schematic diagram showing the curve of the elastic muscle motion diagram provided by the embodiment of the present application.
  • FIG. 9 is a schematic view showing the structure of a device for acquiring muscle biomechanical parameters according to an ultrasonic elastic muscle map according to an embodiment of the present application.
  • Embodiment 1 of the present application provides a method for obtaining muscle biomechanical parameters according to an ultrasonic elastic muscle map, and the method flowchart is as shown in FIG. 1 , and the specific steps are as follows:
  • Synchronous acquisition here means that each muscle dynamic image pair corresponds to an elastic image, that is, the elastic modulus value obtained later changes with the muscle dynamics parameter.
  • the muscle dynamics parameters may include muscle stretching length, muscle strength, strain and joint angle, etc.
  • the corresponding muscle dynamic image sequence may include a displacement image sequence, a muscle force image sequence, a strain image sequence, and a joint angle image sequence,
  • the displacement image sequence is taken as an example for detailed description.
  • the muscle dynamics image includes a displacement image
  • the muscle dynamics parameter includes a muscle stretching length.
  • the single bone is synchronously collected.
  • the subject is required to prohibit violent activities within 2 hours before the test to ensure that the characteristic points of the muscle tissue elongation of the monolithic skeletal muscle of the subject in the initial state can be collected.
  • determining characteristic points of the elongated end of the muscle tissue of the monolithic skeletal muscle includes:
  • the control ultrasonic diagnostic apparatus scans the longitudinal section of the single skeletal muscle along the direction of the muscle bundle through the imaging mode, and uses the detected joint point of the single skeletal muscle and the tendon as a feature point.
  • the initial length here is the length of the monolithic skeletal muscle before stretching, that is, the feature point is located at one end of the single skeletal muscle, and the initial length is the length from one end to the opposite end of the single skeletal muscle.
  • FIG. 3 it is an experimentally acquired sequence of displacement images
  • FIG. 4 is a sequence of elastic images acquired by experiments.
  • step S110 acquiring muscle dynamic parameters corresponding to each muscle dynamic image in the dynamic muscle dynamic image sequence includes the following steps: Figure is shown in Figure 5:
  • the effective values of the displacement change of the feature point position of the feature point in the displacement image relative to the initial state include:
  • the electromyograph is monitored to monitor the myoelectric signals of a single piece of skeletal muscle and surrounding muscle groups.
  • the displacement change of the feature point position in the displacement image relative to the initial state is taken as an effective value.
  • the EMG signals of the measured single skeletal muscles and surrounding muscle groups are monitored during the test.
  • the amplitude of the myoelectric signal is less than 1% of the maximum contraction amplitude, the collection is considered The displacement change is recorded as an effective value.
  • the muscle stretching length l is calculated according to the following formula (1):
  • step S100 that is, before the dynamic muscle dynamic image sequence and the dynamic elastic image sequence in the continuous acquisition of a single skeletal muscle continuous stretching
  • the method further includes:
  • the muscle abdomen position of the monolithic skeletal muscle is determined to acquire the dynamic elastic image sequence at the muscle belly position.
  • the position of the muscle abdomen of the monolithic skeletal muscle is determined as follows:
  • the control ultrasonic diagnostic apparatus scans a transverse section of the skeletal muscle perpendicular to the direction of the muscle bundle by an imaging mode, and positions the largest cross section as the muscle abdomen position of the single skeletal muscle.
  • the imaging mode of the ultrasonic diagnostic apparatus is scanned to scan the cross section of the skeletal muscle muscle bundle perpendicularly, and the probe of the ultrasonic diagnostic apparatus is rotated at the position corresponding to the largest cross section, and the skeletal muscle length is examined along the longitudinal section of the muscle bundle direction.
  • the axis starts the elastography mode to obtain the elastic modulus value corresponding to each elastic image in the dynamic elastic image sequence.
  • the obtaining the elastic modulus value corresponding to each elastic image in the elastic image sequence includes the following steps, as shown in FIG. 6 .
  • the dynamic elastic image sequence of the skeletal muscle during continuous stretching is output along the muscle bundle direction at the muscle abdomen position of the single skeletal muscle.
  • the control ultrasonic diagnostic apparatus quantitatively analyzes a set region in each elastic image in the dynamic elastic image sequence by using an analysis mode, and obtains an elastic modulus value corresponding to each dynamic elastic image.
  • the control super-invigorating device After controlling the position of the muscle abdomen of the skeletal muscle, the control super-invigorating device starts the elastography mode, fixes the probe position, and outputs the dynamic elastic image sequence of the measured skeletal muscle when continuously stretched according to the set frequency, as shown in FIG. 4 .
  • the region of interest of each elastic image that is, the test area, for example, a region of 10 mm ⁇ 10 mm
  • the analysis mode of the ultrasonic diagnostic apparatus is started to quantitatively analyze the region, and the elastic modulus value corresponding to each elastic image is output.
  • the measurement subject when measuring the tensile length of the muscle of the skeletal muscle to be tested and the elastic modulus value corresponding to the tensile length of the muscle, in order to reduce the measurement error, the measurement subject may be taken multiple times and taken multiple times. The average is taken as the final measurement, such as 3 measurements.
  • step S120 that is, using the muscle dynamics parameter as the abscissa, and generating the ultrasonic elastic muscle with the synchronous elastic modulus value as the ordinate.
  • the method further includes:
  • the ultrasound elastic muscle map curve is consistent with the set mechanical model curve. If it is consistent, the step of estimating the muscle biomechanical parameters according to the ultrasound elastic muscle motion curve is performed.
  • the step of estimating muscle biomechanical parameters from the ultrasound elastic myocardus curve After the muscle stretching length is plotted on the abscissa and the elastic modulus curve is generated on the ordinate by the elastic modulus value, according to the shape of the curve, it is judged whether it is consistent with the set mechanical model curve, and when the anastomosis is performed, the follow-up is performed.
  • the step of estimating muscle biomechanical parameters from the ultrasound elastic myocardus curve After the muscle stretching length is plotted on the abscissa and the elastic modulus curve is generated on the ordinate by the elastic modulus value, according to the shape of the curve, it is judged whether it is consistent with the set mechanical model curve, and when the anastomosis is performed, the follow-up is performed.
  • the step of estimating muscle biomechanical parameters from the ultrasound elastic myocardus curve After the muscle stretching length is plotted on the abscissa and the elastic modulus curve is generated on the ordinate by the elastic modulus value, according to the shape of the curve
  • the muscle dynamics image includes a displacement image
  • the muscle dynamic image includes a displacement image
  • the muscle is estimated according to the ultrasound elastic muscle motion curve.
  • the biomechanical parameters include the following steps, and the flow chart is shown in Figure 7:
  • S500 obtains a model formula corresponding to the ultrasonic elastic muscle motion curve and various parameters in the model formula.
  • the hardness index of the single skeletal muscle is determined according to the Gauss-Newton iteration method for the model formula.
  • the relaxed state of a single piece of skeletal muscle refers to a state in which the muscle strength is zero during the stretching of the single piece of skeletal muscle from the initial state, in which the elastic modulus of the single piece of skeletal muscle is almost unchanged. .
  • the elastic modulus curve is generated by the elastic modulus value on the ordinate as shown in Fig. 8.
  • the model formula corresponding to the ultrasonic elastic muscle map curve is as shown in the following formula (2). Show:
  • E 0 is the relaxation elastic modulus value of muscle tissue
  • l 0 is the length of muscle relaxation
  • ⁇ is the hardness index
  • k is the proportional coefficient
  • the elastic modulus corresponding to the ordinate in the elastic muscle map is relaxed in the muscle.
  • the state is always flat and unchanged, and its significantly increased change node, that is, the length of the abscissa corresponding to the muscle strength is started as the estimated value of l 0 , as shown in Figure 8; the abscissa of the elastic muscle map is less than l
  • the mean value E mean of all measured elastic moduli corresponding to the interval of 0 is taken as the estimated value of E 0 , as shown in Fig.
  • the elongation l e is defined as the measured maximum tensile length l max - l 0 ; ⁇ needs to be from the abscissa Estimated in the sequence interval (l ⁇ l 0 ) greater than or equal to l 0 , the specific steps are as follows:
  • the initial parameters usually do not satisfy the minimum sum of the squares of the errors.
  • a 0 By adjusting the coefficient a 0 to minimize the sum of the squares of the errors, and the improved coefficient is a 1 , then:
  • the above equations use Gaussian elimination to solve ⁇ a, and then calculate the value of a 1 . Finally, the calculated a 1 is used as the initial value. The above steps are repeated, and the iteration is repeated and the value of ⁇ a is repeated until the norm of ⁇ a is smaller than A specified threshold.
  • the figure is an elastic muscle map of a normal human gastrocnemius muscle.
  • the extension length of a single skeletal muscle is plotted on the abscissa, and the corresponding elastic modulus value is plotted on the ordinate.
  • the muscle relaxation elastic modulus is estimated from the figure.
  • Embodiment 2 of the present application provides an apparatus for acquiring muscle biomechanical parameters according to an ultrasound elastic muscle map. As shown in FIG. 9, the method includes: an acquisition module 901, an acquisition module 902, and a determination module 903.
  • the collecting module 901 is configured to synchronously acquire a dynamic muscle dynamic image sequence and a dynamic elastic image sequence when the single skeletal muscle is continuously stretched.
  • the obtaining module 902 is configured to respectively acquire the muscle dynamic parameters corresponding to the respective muscle dynamic images in the dynamic muscle dynamic image sequence, and the elastic modulus values corresponding to the elastic images in the dynamic elastic image sequence.
  • the determining module 903 is configured to generate the ultrasonic elastic muscle motion curve with the muscle dynamics parameter as the abscissa and the synchronous elastic modulus value as the ordinate, and estimate the muscle biomechanical parameter according to the ultrasonic elastic muscle motion curve.
  • the muscle dynamics image comprises a displacement image
  • the muscle dynamics parameter comprises a muscle stretching length
  • the acquisition module 901 precedes the dynamic muscle dynamic image sequence and the dynamic elastic image sequence when the single piece of skeletal muscle is continuously stretched. Also used for:
  • the characteristic points of the elongated end of the muscle tissue of the monolithic skeletal muscle in the initial state are determined.
  • the distance from the feature point to the opposite end of the elongated end of the muscle tissue of the monolithic skeletal muscle is calculated to obtain the initial length of the skeletal muscle.
  • the collection module 901 is specifically configured to:
  • the control ultrasonic diagnostic apparatus scans the longitudinal section of the single skeletal muscle along the direction of the muscle bundle by an imaging mode, and uses the detected joint point of the single skeletal muscle and the tendon as a feature point.
  • the obtaining module 902 is specifically configured to:
  • the sum of the effective values of the initial length and the displacement change is recorded as the muscle stretch length corresponding to the displacement image.
  • the acquisition module 902 determines the valid values in the following manner:
  • the electromyograph is monitored to monitor the myoelectric signals of a single piece of skeletal muscle and surrounding muscle groups.
  • the displacement change of the feature point position in the displacement image relative to the initial state is taken as an effective value.
  • the acquisition module 901 is further configured to: before synchronously acquiring the dynamic muscle dynamic image sequence and the dynamic elastic image sequence when the single skeletal muscle is continuously stretched:
  • the muscle abdomen position of the monolithic skeletal muscle is determined to acquire the dynamic elastic image sequence at the muscle belly position.
  • the acquisition module 901 determines the position of the muscle belly of the monolithic skeletal muscle according to the following manner:
  • the control ultrasonic diagnostic apparatus scans the cross section of the skeletal muscle perpendicular to the direction of the muscle bundle by the imaging mode, and the position of the largest cross section is the muscle abdomen position of the single skeletal muscle.
  • the acquisition module 902 obtains the elastic modulus value in the following manner:
  • a dynamic elastic image sequence of the skeletal muscle during continuous stretching is output in the muscle bundle direction at the muscle abdomen position of the monolithic skeletal muscle.
  • the control ultrasonic diagnostic apparatus quantitatively analyzes the set regions in each elastic image in the dynamic elastic image sequence by the analysis mode, and obtains the elastic modulus values corresponding to the dynamic elastic images.
  • the determining module 903 estimates the muscle biomechanical parameters according to the ultrasonic elastic muscle motion curve after the ultrasound elastic muscle map is generated by using the muscle dynamics parameter as the abscissa and the synchronous elastic modulus value as the ordinate. Previously, it was also used to:
  • the ultrasonic elastic muscle map curve is consistent with the set mechanical model curve, and if it is matched, the step of estimating the muscle biomechanical parameters according to the ultrasonic elastic muscle motion curve is performed.
  • the muscle dynamics image comprises a displacement image
  • the muscle dynamics parameter comprising a muscle stretch length
  • the determination module 903 estimates the muscle biomechanical parameters in the following manner:
  • the length of the single skeletal muscle in a relaxed state, the elastic modulus value corresponding to the length of the single skeletal muscle in a relaxed state, and the elongation of the single skeletal muscle are determined according to parameters, and the elongation is a single skeletal muscle.
  • the model formula is used to determine the hardness index of the single skeletal muscle according to the Gauss Newton iteration method.
  • the embodiment of the present application acquires the dynamic muscle dynamic image sequence and the dynamic elastic image sequence when the single skeletal muscle is continuously stretched, and respectively obtains the corresponding muscle dynamic image in the muscle dynamic image sequence.
  • the muscle biomechanical parameters are estimated according to the ultrasound elastogram curve. It can be seen that the muscle dynamic parameters and the elastic modulus values obtained in the embodiments of the present application are measured when the single skeletal muscle is continuously stretched. The parameters of the change, and finally the ultrasound elastic myocardus curve, can be used to estimate the biomechanical parameters of the single skeletal muscle during continuous stretching, and the biomechanical parameters thus obtained are dynamic and quantitative.
  • a computer program product for obtaining muscle biomechanical parameters according to an ultrasound elastic myocardogram provided by an embodiment of the present application, comprising a computer readable storage medium storing program code, the program code comprising instructions for performing the foregoing method
  • the program code comprising instructions for performing the foregoing method
  • the device for obtaining muscle biomechanical parameters according to the ultrasonic elastic myocardogram provided by the embodiment of the present application may be specific hardware on the device or software or firmware installed on the device.
  • the implementation principle and the technical effects of the device provided by the embodiment of the present application are the same as those of the foregoing method embodiment.
  • a person skilled in the art can clearly understand that for the convenience and brevity of the description, the specific working processes of the foregoing system, the device and the unit can refer to the corresponding processes in the foregoing method embodiments, and details are not described herein again.
  • the disclosed apparatus and method may be implemented in other manners.
  • the device embodiments described above are merely illustrative.
  • the division of the unit is only a logical function division.
  • multiple units or components may be combined or Can be integrated into another system, or some features can be ignored or not executed.
  • the mutual coupling or direct coupling or communication connection shown or discussed may be an indirect coupling or communication connection through some communication interface, device or unit, and may be electrical, mechanical or otherwise.
  • the units described as separate components may or may not be physically separated, and the components displayed as units may or may not be physical units, that is, may be located in one place, or may be distributed to multiple network units. Some or all of the units may be selected according to actual needs to achieve the purpose of the solution of the embodiment.
  • each functional unit in the embodiment provided by the present application may be integrated into one processing unit, or each unit may exist physically separately, or two or more units may be integrated into one unit.
  • the functions may be stored in a computer readable storage medium if implemented in the form of a software functional unit and sold or used as a standalone product.
  • the technical solution of the present application which is essential or contributes to the prior art, or a part of the technical solution, may be embodied in the form of a software product, which is stored in a storage medium, including
  • the instructions are used to cause a computer device (which may be a personal computer, server, or network device, etc.) to perform all or part of the steps of the methods described in various embodiments of the present application.
  • the foregoing storage medium includes: a U disk, a mobile hard disk, a read-only memory (ROM), a random access memory (RAM), a magnetic disk, or an optical disk, and the like. .

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Abstract

本申请提供了一种根据超声弹性肌动图获取生物力学参数的方法及装置，其中，该方法包括：同步采集单块骨骼肌连续拉伸时的动态肌肉动力学图像序列和动态弹性图像序列；分别获取所述动态肌肉动力学图像序列中各肌肉动力学图像对应的肌肉动力学参数，以及，所述动态弹性图像序列中各弹性图像对应的弹性模量值；以所述肌肉动力学参数为横坐标，以同步的所述弹性模量值为纵坐标生成超声弹性肌动图曲线，根据所述超声弹性肌动图曲线估算肌肉生物力学参数。本申请能够获得动态变化的生物力学参数，且获得的肌肉生物力学参数精确度较高。

Description

一种根据超声弹性肌动图获取生物力学参数的方法及装置
相关申请的交叉引用
本申请要求于2017年12月12日提交中国专利局的申请号为201711322506.4、名称为“一种根据超声弹性肌动图获取生物力学参数的方法及装置”的中国专利申请的优先权，其全部内容通过引用结合在本申请中。
技术领域
本申请涉及测试技术领域，具体而言，涉及一种根据超声弹性肌动图获取生物力学参数的方法及装置。
背景技术
肌肉是构成人体的重要组织，占体重的40％～45％，分为骨骼肌、平滑肌和心肌三种类型，分布在各器官和骨骼的周围，具有不同的构造、力学性质和功能。骨肌系统依靠肌肉的约束力保持稳定，依靠肌肉的驱动力形成行为运动，在人体运动中扮演者至关重要的作用。
目前，对于肌肉生物力学参数的测试主要是基于超声剪切波弹性成像技术来完成的，超声剪切波弹性成像技术实现了对肌肉组织弹性真正的定量测量，其基本原理是：由超声换能器产生的辐射力在聚焦位置附近产生剪切波，然后测量剪切波在组织中的传播速度，计算出组织的弹性模量。
但是，现有技术中，主要是基于超声剪切波弹性成像技术按照以下方式测量肌肉生物力学参数的：(1)测量松弛状态下骨骼肌的弹性模量值，通过单一的弹性模量值差异评估，肌肉是人体完成各种动作的动力来源，运动过程中肌肉力会引起弹性模量变化，肌肉松弛状态下的弹性模量值智能反映肌力为零时的硬度，无法充分表征其生物力学特性。(2)分别测量松弛状态和紧张状态(主动收缩)下骨骼肌的弹性模量值，用以评估肌肉的功能、张力情况，但是主动收缩产生肌力难以做出定量的评估。(3)测量不同关节角度下骨骼肌的弹性模量值，研究拉伸状态下肌肉租住的生物力学特性，但是不同的关节角度仍然是定性的指标参数，因人而异，不能对肌力做出定量的评估。
综上，现有的基于超声剪切波弹性成像技术测试肌肉生物力学参数的方法无法获取动态信息， 且无法定量获取，所以获得的肌肉生物力学参数精确度不高。
发明内容
有鉴于此，本申请的目的在于提供一种肌肉生物力学参数的测试方法及装置，获取动态变化的生物力学参数及提高获取肌肉生物力学参数的精确度。
第一方面，本申请实施提供了一种根据超声弹性肌动图获取生物力学参数的方法，包括：
同步采集单块骨骼肌连续拉伸时的动态肌肉动力学图像序列和动态弹性图像序列；
分别获取所述动态肌肉动力学图像序列中各肌肉动力学图像对应的肌肉动力学参数，以及，所述动态弹性图像序列中各弹性图像对应的弹性模量值；
以所述肌肉动力学参数为横坐标，以同步的所述弹性模量值为纵坐标生成超声弹性肌动图曲线，根据所述超声弹性肌动图曲线估算肌肉生物力学参数。
结合第一方面，本申请实施例提供了第一方面的第一种可能的实施方式，所述肌肉动力学图像包括位移图像，所述肌肉动力学参数包括肌肉拉伸长度，在所述同步采集单块骨骼肌连续拉伸时的动态肌肉动力学图像序列和动态弹性图像序列之前，所述方法还包括：
确定初始状态下所述单块骨骼肌的肌肉组织伸长端的特征点；
计算所述特征点至所述单块骨骼肌的肌肉组织伸长端的对端的距离，得到所述骨骼肌的初始长度。
结合第一方面的第一种可能的实施方式，本申请实施提供了第一方面的第二种可能的实施方式，确定所述单块骨骼肌的肌肉组织伸长端的特征点包括：
控制超声诊断仪通过成像模式扫描所述单块骨骼肌沿肌束方向的纵切面，将检测到的所述单块骨骼肌与肌腱的结合点作为所述特征点。
结合第一方面的第一种可能的实施方式或第一方面的第二种可能的实施方式，本申请实施提供了第一方面的第三种可能的实施方式，所述获取所述动态肌肉动力学图像序列中各肌肉动力学图像对应的肌肉动力学参数包括：
获取所述特征点在所述位移图像中相对初始状态下的特征点位置的位移变化的有效值；
将所述初始长度和所述位移变化的有效值之和记为所述位移图像对应的肌肉拉伸长度。
结合第一方面的第三种可能的实施方式，本申请实施提供了第一方面的第四种可能的实施方式，所述获取所述特征点在所述位移图像中相对初始状态下的特征点位置的位移变化的有效值包括：
控制肌电仪监控所述单块骨骼肌及周围肌群的肌电信号；
当所述肌电信号的幅值小于设定值时，将所述位移图像中相对初始状态下的特征点位置的位移变化作为所述有效值。
结合第一方面，本申请实施提供了第一方面的第五种可能的实施方式，在所述同步采集单块骨骼肌连续拉伸时的动态肌肉动力学图像序列和动态弹性图像序列之前，所述方法还包括：
确定所述单块骨骼肌的肌腹位置，以在所述肌腹位置处采集所述动态弹性图像序列。
结合第一方面的第五种可能的实施方式，本申请实施提供了第一方面的第六种可能的实施方式，所述确定所述单块骨骼肌的肌腹位置，包括：
控制超声诊断仪通过成像模式扫描所述骨骼肌中垂直于肌束方向的横切面，将横切面最大的位置作为所述单块骨骼肌的肌腹位置。
结合第一方面的第五种可能的实施方式或第一方面的第六种可能的实施方式，本申请实施提供了第一方面的第七种可能的实施方式，所述获取动态弹性图像序列中各动态弹性图像对应的弹性模量值，包括：
在所述单块骨骼肌的肌腹位置沿肌束方向输出所述骨骼肌在连续拉伸时的所述动态弹性图像序列；
控制所述超声诊断仪通过分析模式对所述动态弹性图像序列中的每一幅弹性图像中的设定区域进行定量分析后，得到各弹性图像对应的弹性模量值。
结合第一方方面至第一方面的第二种可能的实施方式、第一方面的第五种可能的实施方式或第一方面的第六种可能的实施方式中的任一项，本申请实施例提供了第一方面的第八种可能的实施方式，在所述以所述肌肉动力学参数为横坐标，以同步的所述弹性模量值为纵坐标生成超声弹性肌动图曲线之后，根据所述超声弹性肌动图曲线估算肌肉生物力学参数之前，所述方法还包括：
确定所述超声弹性肌动图曲线与设定的力学模型曲线是否吻合，若吻合，执行所述根据所述超声弹性肌动图曲线估算肌肉生物力学参数的步骤。
结合第一方面的八种可能的实施方式，本申请实施例提供了第一方面的第九种可能的实施方式，所述肌肉动力学图像包括位移图像，所述肌肉动力学参数包括肌肉拉伸长度，所述根据所述超声弹性肌动图曲线估算肌肉生物力学参数包括：
获取所述超声弹性肌动图曲线对应的模型公式，以及所述模型公式中的各个参数；
根据所述参数确定所述单块骨骼肌在松弛状态下的长度、与所述单块骨骼肌在松弛状态下的长度对应的弹性模量值以及所述单块骨骼肌的延展度，所述延展度为所述单块骨骼肌的最大拉伸长度与所述单块骨骼肌在松弛状态下的长度之差；
在所述骨骼肌长度大于所述单块骨骼肌在松弛状态下的长度时，对所述模型公式按照高斯牛顿迭代法，确定所述单块骨骼肌的硬度指标。
第二方面，本申请实施例提供了一种根据超声弹性肌动图获取肌肉生物力学参数的装置，包括：
采集模块，用于同步采集单块骨骼肌连续拉伸时的动态肌肉动力学图像序列和动态弹性图像序列；
获取模块，用于分别获取所述动态肌肉动力学图像序列中各肌肉动力学图像对应的肌肉动力学参数，以及，所述动态弹性图像序列中各弹性图像对应的弹性模量值；
确定模块，用于以所述肌肉动力学参数为横坐标，以同步的所述弹性模量值为纵坐标生成超声弹性肌动图曲线，根据所述超声弹性肌动图曲线估算肌肉生物力学参数。
与现有技术相比，本申请实施例是通过同步采集单块骨骼肌连续拉伸时的动态肌肉动力学图像序列和动态弹性图像序列，分别获取肌肉动力学图像序列中各肌肉动力学图像对应的肌肉动力学参数，以及，动态弹性图像序列中各动态弹性图像对应的弹性模量值；以所述肌肉动力学参数为横坐标，以同步的所述弹性模量值为纵坐标生成超声弹性肌动图曲线，根据所述超声弹性肌动图曲线估算肌肉生物力学参数，可见，本申请获得的肌肉动力学参数和弹性模量值是在单块骨骼肌连续拉伸时测得的变化参数，且最终生超声弹性肌动图曲线，可以由该曲线估算单块骨骼肌在连续拉伸过程 中的生物力学参数，这样得到的生物力学参数是动态的且是定量的。
为使本申请的上述目的、特征和优点能更明显易懂，下文特举较佳实施例，并配合所附附图，作详细说明如下。
附图说明
为了更清楚地说明本申请实施例的技术方案，下面将对实施例中所需要使用的附图作简单地介绍，应当理解，以下附图仅示出了本申请的某些实施例，因此不应被看作是对范围的限定，对于本领域普通技术人员来讲，在不付出创造性劳动的前提下，还可以根据这些附图获得其他相关的附图。
图1示出了本申请实施例所提供的一种根据超声弹性肌动图获取肌肉生物力学参数的方法流程图；
图2示出了本申请实施例所提供的一种获取骨骼肌初始长度的方法流程图；
图3示出了本申请实施例所提供的一种位移图像序列图；
图4示出了本申请实施例所提供的一种弹性模量序列图；
图5示出了本申请实施例所提供的一种获取骨骼肌肌肉拉伸长度方法流程图；
图6示出了本申请实施例所提供的得到各动态弹性图像对应的弹性模量值流程图；
图7示出了本申请实施例所提供的估算肌肉生物力学参数的方法流程图；
图8示出了本申请实施例所提供的弹性肌动图曲线示意图；
图9示出了本申请实施例所提供一种根据超声弹性肌动图获取肌肉生物力学参数的装置结构示意图。
具体实施方式
为使本申请实施例的目的、技术方案和优点更加清楚，下面将结合本申请实施例中附图，对本申请实施例中的技术方案进行清楚、完整地描述，显然，所描述的实施例仅仅是本申请一部分实施例，而不是全部的实施例。通常在此处附图中描述和示出的本申请实施例的组件可以以各种不同的配置来布置和设计。因此，以下对在附图中提供的本申请的实施例的详细描述并非旨在限制要求保 护的本申请的范围，而是仅仅表示本申请的选定实施例。基于本申请的实施例，本领域技术人员在没有做出创造性劳动的前提下所获得的所有其他实施例，都属于本申请保护的范围。
实施例1
本申请实施例1提供了一种根据超声弹性肌动图获取肌肉生物力学参数的方法，其方法流程图如图1所述，具体步骤如下：
S100，同步采集单块骨骼肌连续拉伸时的动态肌肉动力学图像序列和动态弹性图像序列。
这里的同步采集，是指每一幅肌肉动力学图像对对应一幅弹性图像，即使得之后获取的弹性模量值随着肌肉动力学参数的变化而变化。
S110，分别获取动态肌肉动力学图像序列中各肌肉动力学图像对应的肌肉动力学参数，以及，动态弹性图像序列中各弹性图像对应的弹性模量值。
S120，以肌肉动力学参数为横坐标，以同步的弹性模量值为纵坐标生成超声弹性肌动图曲线，根据超声弹性肌动图曲线估算肌肉生物力学参数。
其中，肌肉动力学参数可以包括肌肉拉伸长度、肌力、应变和关节角度等，相应的肌肉动力学图像序列可以包括位移图像序列、肌力图像序列、应变图像序列和关节角度图像序列，本申请实施例中以位移图像序列为例进行详细说明。
一种较佳的实施方式，在本申请实施例1提出的技术方案中，肌肉动力学图像包括位移图像，肌肉动力学参数包括肌肉拉伸长度，在S100步骤中，即在同步采集单块骨骼肌连续拉伸时的动态肌肉动力学图像序列和动态弹性图像序列之前，该方法还包括如下步骤，流程图如图2所示：
S200，确定初始状态下单块骨骼肌的肌肉组织伸长端的特征点。
要求被测者在测试前2小时内禁止进行剧烈活动，确保能够采集到被测者在初始状态下的单块骨骼肌的肌肉组织伸长端的特征点。
可选地，确定单块骨骼肌的肌肉组织伸长端的特征点包括：
控制超声诊断仪通过成像模式扫描单块骨骼肌沿肌束方向的纵切面，将检测到的单块骨骼肌与肌腱的结合点作为特征点。
S210，计算特征点至单块骨骼肌的肌肉组织伸长端的对端的距离，得到骨骼肌的初始长度。
这里的初始长度即单块骨骼肌在拉伸前的长度，即特征点位于该单块骨骼肌两端的一个端点，初始长度为该单块骨骼肌的一个端点到对端的长度。
如图3所示，即为实验获取的位移图像序列，以及，图4为实验同步获取的弹性图像序列。
一种较佳的实施方式，在本申请实施例1提出的技术方案中，在步骤S110中，即获取动态肌肉动力学图像序列中各肌肉动力学图像对应的肌肉动力学参数包括以下步骤，流程图如图5所示：
S300，获取特征点在位移图像中相对初始状态下的特征点位置的位移变化的有效值。
其中，获取特征点在位移图像中相对初始状态下的特征点位置的位移变化的有效值包括：
控制肌电仪监控单块骨骼肌及周围肌群的肌电信号。
当肌电信号的幅值小于设定值时，将位移图像中相对初始状态下的特征点位置的位移变化作为有效值。
为了避免被测者肌肉无意识主动收缩产生伪像，测试时采集被测单块骨骼肌及周围肌群的肌电信号进行监控，当肌电信号幅度小于最大收缩时幅度的1％时，认为采集的位移变化作为有效值进行记录。
S310，将初始长度和位移变化的有效值之和记为位移图像对应的肌肉拉伸长度。
若初始长度记为l init,位移变化的有效值记为Δl，则肌肉拉伸长度l按照以下公式(1)计算：
l＝l init+Δl                                              (1)
一种较佳的实施方式，在本申请实施例1提出的技术方案中，在步骤S100中，即在同步采集单块骨骼肌连续拉伸时的动态肌肉动力学图像序列和动态弹性图像序列之前，该方法还包括：
确定单块骨骼肌的肌腹位置，以在肌腹位置处采集所述动态弹性图像序列。
按照以下方式确定所述单块骨骼肌的肌腹位置：
控制超声诊断仪通过成像模式扫描所述骨骼肌中垂直于肌束方向的横切面，将横切面最大的位置作为所述单块骨骼肌的肌腹位置。
本申请实施例中控制超声诊断仪的成像模式扫查垂直与待测骨骼肌肌束的横截面，在最大横截面对应的位置旋转超声诊断仪的探头，沿肌束方向纵切面检查骨骼肌长轴，启动弹性成像模式来获取动态弹性图像序列中各弹性图像对应的弹性模量值。
其中，获取弹性图像序列中各弹性图像对应的弹性模量值，包括以下步骤，如图6所示为其流程示意图：
S400，在单块骨骼肌的肌腹位置沿肌束方向输出骨骼肌在连续拉伸时的动态弹性图像序列。
S410，控制超声诊断仪通过分析模式对动态弹性图像序列中的每一幅弹性图像中的设定区域进行定量分析后，得到各动态弹性图像对应的弹性模量值。
控制超生诊断仪在找到骨骼肌的肌腹位置后，启动弹性成像模式，固定探头位置，按照设定频率输出被测骨骼肌在被连续拉伸时的动态弹性图像序列，如图4所示，在确立每一幅弹性图像的感兴趣区即测试区，比如10mm×10mm的区域后,启动超声诊断仪的分析模式对该区域进行定量分析后，输出与各弹性图像对应的弹性模量值。
较佳地，在测量待测单块骨骼肌的肌肉拉伸长度以及对该肌肉拉伸长度对应的弹性模量值时，为了降低测量误差，可以采取测量被测者多次，取多次的平均值作为最终的测量结果，比如测量3次。
一种较佳的实施方式，在本申请实施例1提出的技术方案中，在步骤S120中，即在以肌肉动力学参数为横坐标，以同步的弹性模量值为纵坐标生成超声弹性肌动图曲线之后，根据超声弹性肌动图曲线估算肌肉生物力学参数之前，该方法还包括：
确定超声弹性肌动图曲线与设定的力学模型曲线是否吻合，若吻合，执行根据超声弹性肌动图曲线估算肌肉生物力学参数的步骤。
在以肌肉拉伸长度为横坐标，以弹性模量值以纵坐标生成超声弹性肌动图曲线后，根据该曲线的形状，判断是否与设定的力学模型曲线吻合，在吻合时，执行后续的根据超声弹性肌动图曲线估算肌肉生物力学参数的步骤。
一种较佳的实施方式，在本申请实施例1提出的技术方案中，肌肉动力学图像包括位移图像， 肌肉动力学图像包括位移图像，在步骤S120中，根据超声弹性肌动图曲线估算肌肉生物力学参数包括以下步骤，流程图如图7所示：
S500，获取超声弹性肌动图曲线对应的模型公式，以及模型公式中的各个参数。
S510，根据参数确定单块骨骼肌在松弛状态下的长度、与单块骨骼肌在松弛状态下的长度对应的弹性模量值以及单块骨骼肌的延展度，延展度为单块骨骼肌的最大拉伸长度与所述单块骨骼肌在松弛状态下的长度之差。
S520，在骨骼肌长度大于单块骨骼肌在松弛状态下的长度时，对模型公式按照高斯牛顿迭代法，确定单块骨骼肌的硬度指标。
单块骨骼肌的松弛状态是指该单块骨骼肌从初始状态开始被拉伸过程中，肌力为零的一个状态，在该松弛状态下，该单块骨骼肌的弹性模量几乎不变。
在以肌肉拉伸长度为横坐标，以弹性模量值以纵坐标生成超声弹性肌动图曲线如图8所示，得到的该超声弹性肌动图曲线对应的模型公式如下式(2)所示：
E＝E 0；l≤l 0；
Figure PCTCN2017118725-appb-000001
上式中，E 0为肌肉组织松弛弹性模量值；l 0为肌肉松弛长度；α为硬度指标；k为比例系数；弹性肌动图曲线中纵坐标对应的弹性模量值在肌肉处于松弛状态时一直是平坦不变的，其显著增大的变化结点，即开始产生肌力对应的横坐标长度作为l 0的估计值，如图8所示；弹性肌动图中横坐标小于l 0的区间对应的所有测量弹性模量的均值E mean作为E 0的估计值，如图8所示；延展度l e定义为测量的最大拉伸长度l max-l 0；α需要从横坐标大于等于l 0序列区间(l≥l 0)中估计出来，具体步骤如下：
令
Figure PCTCN2017118725-appb-000002
其中需要估计的未知参数为a＝[α,k]，使用最小二乘判别原则，采用基于泰勒级数的迭代法，记初始的试验系数为a 0，即：
y＝f(x,a 0)；                                                (4)
初始参数通常不满足误差的平方和最小，通过调整系数a 0使误差的平方和最小，记改进的系数为a 1，则有：
a 1＝a 0+△a；                                                     (5)
将公式(5)代入公式(4)得到：
y＝f(x,a 1)＝f(x,a 0+△a)；                                       (6)
将函数按泰勒级数展开，保留一阶导数项，得到：
Figure PCTCN2017118725-appb-000003
令f 1 0＝f(x i,a 0)，与y i之间的误差为：
Figure PCTCN2017118725-appb-000004
误差的平方和为：
Figure PCTCN2017118725-appb-000005
需要求误差平方和的极小值，则：
Figure PCTCN2017118725-appb-000006
即：
Figure PCTCN2017118725-appb-000007
可用矩阵记号表示为：K(△a)＝b                                (12)
其中△a的元素为Δa p(p＝0,1)，且:
Figure PCTCN2017118725-appb-000008
上述方程组采用高斯消元法求解△a，继而算出a 1的值，最后，将算得的a 1作为初值，重复上述步骤，反复迭代和修正△a的值，直至△a的范数小于一个指定的阈值。
由图8所示，该图为正常人腓肠肌的弹性肌动图，以单块骨骼肌的伸展长度为横坐标，以对应 的弹性模量值为纵坐标，从图中估计出肌肉松弛弹性模量E 0＝8.5kPa；松弛长度l 0＝0.427m；延展度l e＝0.026m；硬度指标α＝158.8。
实施例2
本申请实施例2提供了一种根据超声弹性肌动图获取肌肉生物力学参数的装置，如图9所示，包括：采集模块901、获取模块902和确定模块903。
采集模块901，用于同步采集单块骨骼肌连续拉伸时的动态肌肉动力学图像序列和动态弹性图像序列。
获取模块902，用于分别获取动态肌肉动力学图像序列中各肌肉动力学图像对应的肌肉动力学参数，以及，动态弹性图像序列中各弹性图像对应的弹性模量值。
确定模块903，用于以所述肌肉动力学参数为横坐标，以同步的弹性模量值为纵坐标生成超声弹性肌动图曲线，根据超声弹性肌动图曲线估算肌肉生物力学参数。
较佳地，肌肉动力学图像包括位移图像，肌肉动力学参数包括肌肉拉伸长度，采集模块901在同步采集单块骨骼肌连续拉伸时的动态肌肉动力学图像序列和动态弹性图像序列之前，还用于：
确定初始状态下单块骨骼肌的肌肉组织伸长端的特征点。
计算特征点至单块骨骼肌的肌肉组织伸长端的对端的距离，得到骨骼肌的初始长度。
较佳地，采集模块901具体用于：
控制超声诊断仪通过成像模式扫描所述单块骨骼肌沿肌束方向的纵切面，将检测到的单块骨骼肌与肌腱的结合点作为特征点。
较佳地，获取模块902具体用于：
获取特征点在位移图像中相对初始状态下的特征点位置的位移变化的有效值。
将初始长度和位移变化的有效值之和记为位移图像对应的肌肉拉伸长度。
较佳地，获取模块902按照以下方式确定有效值：
控制肌电仪监控单块骨骼肌及周围肌群的肌电信号。
当肌电信号的幅值小于设定值时，将位移图像中相对初始状态下的特征点位置的位移变化作为有效值。
较佳地，采集模块901在同步采集单块骨骼肌连续拉伸时的动态肌肉动力学图像序列和动态弹性图像序列之前，还用于：
确定单块骨骼肌的肌腹位置，以在肌腹位置处采集所述动态弹性图像序列。
较佳地，采集模块901具体根据以下方式确定单块骨骼肌的肌腹位置：
控制超声诊断仪通过成像模式扫描所述骨骼肌中垂直于肌束方向的横切面，将横切面最大的位置作为单块骨骼肌的肌腹位置。
较佳地，获取模块902具体按照以下方式获取弹性模量值：
在单块骨骼肌的肌腹位置沿肌束方向输出所述骨骼肌在连续拉伸时的动态弹性图像序列。
控制超声诊断仪通过分析模式对动态弹性图像序列中的每一幅弹性图像中的设定区域进行定量分析后，得到各动态弹性图像对应的弹性模量值。
较佳地，确定模块903在以所述肌肉动力学参数为横坐标，以同步的弹性模量值为纵坐标生成超声弹性肌动图曲线之后，根据超声弹性肌动图曲线估算肌肉生物力学参数之前，还用于：
确定超声弹性肌动图曲线与设定的力学模型曲线是否吻合，若吻合，执行根据所述超声弹性肌动图曲线估算肌肉生物力学参数的步骤。
较佳地，肌肉动力学图像包括位移图像，所述肌肉动力学参数包括肌肉拉伸长度，确定模块903按照以下方式估算肌肉生物力学参数：
获取超声弹性肌动图曲线对应的模型公式，以及模型公式中的各个参数。
根据参数确定所述单块骨骼肌在松弛状态下的长度、与单块骨骼肌在松弛状态下的长度对应的弹性模量值以及单块骨骼肌的延展度，延展度为单块骨骼肌的最大拉伸长度与单块骨骼肌在松弛状态下的长度之差。
在骨骼肌长度大于单块骨骼肌在松弛状态下的长度时，对模型公式按照高斯牛顿迭代法，确定 单块骨骼肌的硬度指标。
与现有技术相比，本申请实施例是通过同步采集单块骨骼肌连续拉伸时的动态肌肉动力学图像序列和动态弹性图像序列，分别获取肌肉动力学图像序列中各肌肉动力学图像对应的肌肉动力学参数，以及，动态弹性图像序列中各动态弹性图像对应的弹性模量值；以所述肌肉动力学参数为横坐标，以同步的所述弹性模量值为纵坐标生成超声弹性肌动图曲线，根据所述超声弹性肌动图曲线估算肌肉生物力学参数，可见，本申请实施例获得的肌肉动力学参数和弹性模量值是在单块骨骼肌连续拉伸时测得的变化参数，且最终生超声弹性肌动图曲线，可以由该曲线估算单块骨骼肌在连续拉伸过程中的生物力学参数，这样得到的生物力学参数是动态的且是定量的。
本申请实施例所提供的进行的根据超声弹性肌动图获取肌肉生物力学参数的方法计算机程序产品，包括存储了程序代码的计算机可读存储介质，所述程序代码包括的指令可用于执行前面方法实施例中所述的方法，具体实现可参见方法实施例，在此不再赘述。
本申请实施例所提供的根据超声弹性肌动图获取肌肉生物力学参数的装置可以为设备上的特定硬件或者安装于设备上的软件或固件等。本申请实施例所提供的装置，其实现原理及产生的技术效果和前述方法实施例相同，为简要描述，装置实施例部分未提及之处，可参考前述方法实施例中相应内容。所属领域的技术人员可以清楚地了解到，为描述的方便和简洁，前述描述的系统、装置和单元的具体工作过程，均可以参考上述方法实施例中的对应过程，在此不再赘述。
在本申请所提供的实施例中，应该理解到，所揭露装置和方法，可以通过其它的方式实现。以上所描述的装置实施例仅仅是示意性的，例如，所述单元的划分，仅仅为一种逻辑功能划分，实际实现时可以有另外的划分方式，又例如，多个单元或组件可以结合或者可以集成到另一个系统，或一些特征可以忽略，或不执行。另一点，所显示或讨论的相互之间的耦合或直接耦合或通信连接可以是通过一些通信接口，装置或单元的间接耦合或通信连接，可以是电性，机械或其它的形式。
所述作为分离部件说明的单元可以是或者也可以不是物理上分开的，作为单元显示的部件可以是或者也可以不是物理单元，即可以位于一个地方，或者也可以分布到多个网络单元上。可以根据实际的需要选择其中的部分或者全部单元来实现本实施例方案的目的。
另外，在本申请提供的实施例中的各功能单元可以集成在一个处理单元中，也可以是各个单元 单独物理存在，也可以两个或两个以上单元集成在一个单元中。
所述功能如果以软件功能单元的形式实现并作为独立的产品销售或使用时，可以存储在一个计算机可读取存储介质中。基于这样的理解，本申请的技术方案本质上或者说对现有技术做出贡献的部分或者该技术方案的部分可以以软件产品的形式体现出来，该计算机软件产品存储在一个存储介质中，包括若干指令用以使得一台计算机设备(可以是个人计算机，服务器，或者网络设备等)执行本申请各个实施例所述方法的全部或部分步骤。而前述的存储介质包括：U盘、移动硬盘、只读存储器(ROM，Read-Only Memory)、随机存取存储器(RAM，Random Access Memory)、磁碟或者光盘等各种可以存储程序代码的介质。
应注意到：相似的标号和字母在下面的附图中表示类似项，因此，一旦某一项在一个附图中被定义，则在随后的附图中不需要对其进行进一步定义和解释，此外，术语“第一”、“第二”、“第三”等仅用于区分描述，而不能理解为指示或暗示相对重要性。
最后应说明的是：以上所述实施例，仅为本申请的具体实施方式，用以说明本申请的技术方案，而非对其限制，本申请的保护范围并不局限于此，尽管参照前述实施例对本申请进行了详细的说明，本领域的普通技术人员应当理解：任何熟悉本技术领域的技术人员在本申请揭露的技术范围内，其依然可以对前述实施例所记载的技术方案进行修改或可轻易想到变化，或者对其中部分技术特征进行等同替换；而这些修改、变化或者替换，并不使相应技术方案的本质脱离本申请实施例技术方案的精神和范围。都应涵盖在本申请的保护范围之内。因此，本申请的保护范围应所述以权利要求的保护范围为准。

Claims (11)

  1. 一种根据超声弹性肌动图获取肌肉生物力学参数的方法，其特征在于，包括：
    同步采集单块骨骼肌连续拉伸时的动态肌肉动力学图像序列和动态弹性图像序列；
    分别获取所述动态肌肉动力学图像序列中各肌肉动力学图像对应的肌肉动力学参数，以及，所述动态弹性图像序列中各弹性图像对应的弹性模量值；
    以所述肌肉动力学参数为横坐标，以同步的所述弹性模量值为纵坐标生成超声弹性肌动图曲线，根据所述超声弹性肌动图曲线估算肌肉生物力学参数。
  2. 根据权利要求1所述的方法，其特征在于，所述肌肉动力学图像包括位移图像，所述肌肉动力学参数包括肌肉拉伸长度，在所述同步采集单块骨骼肌连续拉伸时的动态肌肉动力学图像序列和动态弹性图像序列之前，所述方法还包括：
    确定初始状态下所述单块骨骼肌的肌肉组织伸长端的特征点；
    计算所述特征点至所述单块骨骼肌的肌肉组织伸长端的对端的距离，得到所述骨骼肌的初始长度。
  3. 根据权利要求2所述的方法，其特征在于，确定所述单块骨骼肌的肌肉组织伸长端的特征点包括：
    控制超声诊断仪通过成像模式扫描所述单块骨骼肌沿肌束方向的纵切面，将检测到的所述单块骨骼肌与肌腱的结合点作为所述特征点。
  4. 根据权利要求2或3所述的方法，其特征在于，所述获取所述动态肌肉动力学图像序列中各肌肉动力学图像对应的肌肉动力学参数包括：
    获取所述特征点在所述位移图像中相对初始状态下的特征点位置的位移变化的有效值；
    将所述初始长度和所述位移变化的有效值之和记为所述位移图像对应的肌肉拉伸长度。
  5. 根据权利要求4所述的方法，其特征在于，所述获取所述特征点在所述位移图像中相对初始状态下的特征点位置的位移变化的有效值包括：
    控制肌电仪监控所述单块骨骼肌及周围肌群的肌电信号；
    当所述肌电信号的幅值小于设定值时，将所述位移图像中相对初始状态下的特征点位置的位移变化作为所述有效值。
  6. 根据权利要求1所述的方法，其特征在于，在所述同步采集单块骨骼肌连续拉伸时的动态肌肉动力学图像序列和动态弹性图像序列之前，所述方法还包括：
    确定所述单块骨骼肌的肌腹位置，以在所述肌腹位置处采集所述动态弹性图像序列。
  7. 根据权利要求6所述的方法，其特征在于，所述确定所述单块骨骼肌的肌腹位置，包括：
    控制超声诊断仪通过成像模式扫描所述骨骼肌中垂直于肌束方向的横切面，将横切面最大的位置作为所述单块骨骼肌的肌腹位置。
  8. 根据权利要求6或7所述的方法，其特征在于，所述获取动态弹性图像序列中各弹性图像对应的弹性模量值，包括：
    在所述单块骨骼肌的肌腹位置沿肌束方向输出所述骨骼肌在连续拉伸时的所述动态弹性图像序列；
    控制所述超声诊断仪通过分析模式对所述动态弹性图像序列中的每一幅弹性图像中的设定区域进行定量分析后，得到各弹性图像对应的弹性模量值。
  9. 根据权利要求1至3、6和7任一项所述的方法，其特征在于，在所述以所述肌肉动力学参数为横坐标，以同步的所述弹性模量值为纵坐标生成超声弹性肌动图曲线之后，根据所述超声弹性肌动图曲线估算肌肉生物力学参数之前，所述方法还包括：
    确定所述超声弹性肌动图曲线与设定的力学模型曲线是否吻合，若吻合，执行所述根据所述超声弹性肌动图曲线估算肌肉生物力学参数的步骤。
  10. 根据权利要求9所述的方法，其特征在于，所述肌肉动力学图像包括位移图像，所述肌肉动力学参数包括肌肉拉伸长度，所述根据所述超声弹性肌动图曲线估算肌肉生物力学参数包括：
    获取所述超声弹性肌动图曲线对应的模型公式，以及所述模型公式中的各个参数；
    根据所述参数确定所述单块骨骼肌在松弛状态下的长度、与所述单块骨骼肌在松弛状态下的长度对应的弹性模量值以及所述单块骨骼肌的延展度，所述延展度为所述单块骨骼肌的最大拉伸长度与所述单块骨骼肌在松弛状态下的长度之差；
    在所述骨骼肌长度大于所述单块骨骼肌在松弛状态下的长度时，对所述模型公式按照高斯牛顿迭代法，确定所述单块骨骼肌的硬度指标。
  11. 一种根据超声弹性肌动图获取肌肉生物力学参数的装置，其特征在于，包括：
    采集模块，配置成同步采集单块骨骼肌连续拉伸时的动态肌肉动力学图像序列和动态弹性图像序列；
    获取模块，配置成分别获取所述动态肌肉动力学图像序列中各肌肉动力学图像对应的肌肉动力学参数，以及，所述动态弹性图像序列中各弹性图像对应的弹性模量值；
    确定模块，配置成以所述肌肉动力学参数为横坐标，以同步的所述弹性模量值为纵坐标生成超声弹性肌动图曲线，根据所述超声弹性肌动图曲线估算肌肉生物力学参数。
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