WO2009154117A1 - 筋トーヌス計測装置 - Google Patents
筋トーヌス計測装置 Download PDFInfo
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- WO2009154117A1 WO2009154117A1 PCT/JP2009/060615 JP2009060615W WO2009154117A1 WO 2009154117 A1 WO2009154117 A1 WO 2009154117A1 JP 2009060615 W JP2009060615 W JP 2009060615W WO 2009154117 A1 WO2009154117 A1 WO 2009154117A1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/22—Ergometry; Measuring muscular strength or the force of a muscular blow
- A61B5/224—Measuring muscular strength
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
- A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
- A61B5/1107—Measuring contraction of parts of the body, e.g. organ, muscle
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
- A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
- A61B5/1124—Determining motor skills
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
- A61B5/11—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb
- A61B5/1126—Measuring movement of the entire body or parts thereof, e.g. head or hand tremor, mobility of a limb using a particular sensing technique
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
- A61B5/316—Modalities, i.e. specific diagnostic methods
- A61B5/389—Electromyography [EMG]
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/40—Detecting, measuring or recording for evaluating the nervous system
- A61B5/4076—Diagnosing or monitoring particular conditions of the nervous system
- A61B5/4082—Diagnosing or monitoring movement diseases, e.g. Parkinson, Huntington or Tourette
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/45—For evaluating or diagnosing the musculoskeletal system or teeth
- A61B5/4519—Muscles
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2562/00—Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
- A61B2562/02—Details of sensors specially adapted for in-vivo measurements
- A61B2562/0247—Pressure sensors
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/45—For evaluating or diagnosing the musculoskeletal system or teeth
- A61B5/4528—Joints
Definitions
- the present invention relates to a muscle tonus measuring apparatus for measuring and objectively evaluating muscle tonus characteristics of patients with Parkinson's disease and stroke.
- ⁇ Muscle tonus abnormalities such as spasticity and muscle rigidity that cause an enhanced stretch reflex are caused by pyramidal and extrapyramidal disorders, and are very useful findings as a measure for evaluating the degree of central disorder.
- Modified ⁇ Ashworth Scale is known for spasticity and UPDRS (Unified Parkinson Disease Rating Scale) is known for muscle toughness. Yes, there may be differences between evaluators and intra-evaluator differences. Therefore, development of these quantitative measuring instruments is desired.
- Patent Document 1 and Non-Patent Document 1 describe a mitt type or cuff type muscle strength meter provided with a pair of pressure transducers.
- the evaluator grips the subject's wrist so as to be sandwiched between the pair of pressure transducers, and bends and stretches the subject's elbow.
- the pushing / pulling force that the evaluator applies to the wrist of the subject is measured via a pair of pressure transducers.
- the displacement of the subject's forearm is measured.
- This muscle strength meter is relatively small, and the wearability to the subject is also improved compared to the conventional one.
- An object of the present invention is to solve the above-described conventional problems and to provide a muscle tonus measuring apparatus that can easily and objectively evaluate muscle tonus with a simple configuration.
- the muscle tonus measuring apparatus of the present invention includes at least one force sensor that detects a force applied to bend and extend the subject's joint, and a sensor that measures the joint angle of the subject's joint.
- a joint torque for bending and extending the joint is calculated from the force detected by the force sensor. Then, the temporal change in the joint torque and the joint angle when the subject's joint is flexed and extended is changed to the maximum extension stationary phase, the dynamic flexion phase, the maximum flexion position static phase, and the dynamic extension phase.
- the muscle tonus feature amount is extracted from the relationship between the joint angle and the joint torque in at least one of the dynamic flexion phase and the dynamic extension phase.
- the muscle tonus feature value is extracted from the relationship between the joint angle and the joint torque in at least one of the dynamic flexion phase and the dynamic extension phase of the joint.
- FIG. 1 is a diagram showing a schematic configuration of a muscle tonus measuring apparatus according to an embodiment of the present invention.
- FIG. 2 is a diagram showing a data analysis method in the muscle tonus measuring apparatus according to the embodiment of the present invention.
- FIG. 3A is a representative raw waveform diagram of a muscle tonus measurement result of a healthy person.
- FIG. 3B is an angle-torque characteristic diagram in the dynamic flexion phase and the dynamic extension phase, obtained from the raw waveform diagram of FIG. 3A.
- FIG. 4A is a representative raw waveform diagram of a muscle tonus measurement result of a Parkinson's disease patient (UPDRS 1).
- FIG. 1 is a diagram showing a schematic configuration of a muscle tonus measuring apparatus according to an embodiment of the present invention.
- FIG. 2 is a diagram showing a data analysis method in the muscle tonus measuring apparatus according to the embodiment of the present invention.
- FIG. 3A is a representative raw waveform diagram of a muscle tonus measurement
- FIG. 4B is an angle-torque characteristic diagram in the dynamic flexion phase and the dynamic extension phase, obtained from the raw waveform diagram of FIG. 4A.
- FIG. 5A is a representative raw waveform diagram of a muscle tonus measurement result of a Parkinson's disease patient (UPDRS 2).
- FIG. 5B is an angle-torque characteristic diagram in the dynamic flexion phase and the dynamic extension phase, obtained from the raw waveform diagram of FIG. 5A.
- FIG. 6A is a representative raw waveform diagram of a muscle tonus measurement result of a Parkinson's disease patient (UPDRS 3).
- FIG. 6B is an angle-torque characteristic diagram in the dynamic flexion phase and the dynamic extension phase obtained from the raw waveform diagram of FIG. 6A.
- FIG. 7A is a box-and-whisker diagram showing the dynamic extension phase spring coefficients extracted from the data obtained in the example, classified for each UPDRS.
- FIG. 7B is a box-and-whisker diagram showing the dynamic bending phase spring coefficients extracted from the data obtained in the example, classified for each UPDRS.
- FIG. 7C is a box and whisker plot showing the sum of the bias differences extracted from the data obtained in the example, classified by UPDRS.
- FIG. 7D is a box and whisker plot showing the IEMG ratio of the biceps extracted from the data obtained in the example, classified by UPDRS.
- FIG. 7E is a box and whisker plot showing the IEMG ratio of the triceps extracted from the data obtained in the example, classified by UPDRS.
- FIG. 8 is a box-and-whisker diagram showing IEEM ratios for the biceps brachii obtained in the examples, classified into a healthy subject group and a Parkinson's disease patient group.
- FIG. 9 shows changes over time in torque differentiation obtained by time-differentiating elbow joint torque in the dynamic extension phase for healthy subjects, Parkinson's disease patients (without tremor), and Parkinson's disease patients (with tremor). It is a figure.
- the above-described muscle tonus measuring apparatus of the present invention includes at least one force sensor.
- the force applied to bend the joint of the subject and the force applied to extend the joint may be detected by a common force sensor, or may be detected by separate force sensors.
- the at least one force sensor and the sensor for measuring the joint angle are mounted on a common base. Therefore, since an apparatus can be reduced in size, the mounting property with respect to a test subject improves. Further, since the number of components of the apparatus is reduced, the setup for performing muscle tonus measurement is simplified.
- the senor for measuring the joint angle includes a gyro sensor.
- the gyro sensor can calculate the joint angle by detecting the angular velocity generated along with the bending / extending motion of the joint and integrating the detected angular velocity. Thereby, the measurement of the joint angle can be accurately performed with a simple and small device.
- the muscle tonus feature amount includes a spring coefficient of the joint. Since the spring coefficient of the joint has a correlation with the degree of muscle rigidity, the reliability of the muscle tonus evaluation is improved by using the spring coefficient.
- the spring coefficient is a spring coefficient in the dynamic flexion phase and the dynamic extension phase of the joint. This further improves the reliability of muscle tonus evaluation.
- the muscle tonus feature value is based on the difference between the relationship between the joint angle and the joint torque in the dynamic flexion phase of the joint and the relationship between the joint angle and the joint torque in the dynamic extension phase of the joint. It is preferable to contain. In general, the higher the degree of muscle rigidity, the greater the difference in dynamic dynamics between the dynamic flexion phase and the dynamic extension phase. Therefore, according to this preferable aspect, the reliability of muscle tonus evaluation is improved.
- the muscle tonus measuring apparatus of the present invention further includes a surface electrode for measuring surface myoelectric potential.
- a myoelectric activity feature amount from the surface myoelectric potential in the maximum flexion position stationary phase and maximum extension position stationary phase of the joint.
- the presence or absence of muscle rigidity has a correlation with changes in surface myoelectric potential in the maximum flexion position stationary phase and maximum extension position stationary phase of the joint. Therefore, according to this preferable aspect, a healthy person and a Parkinson's disease patient can be identified with higher accuracy. It is also possible to identify the severity of muscle stiffness in Parkinson's disease patients using myoelectric activity features.
- the muscle tonus measuring apparatus of the present invention further extracts a joint torque feature amount by frequency analysis of the joint torque. Thereby, identification of a healthy person and a Parkinson's disease patient, and the presence or absence of the tremor of a Parkinson's disease patient can be objectively performed.
- the joint is an elbow joint.
- muscle tonus can be objectively evaluated by a method that is closer to the examination procedure that has been performed by doctors in the past.
- FIG. 1 shows a schematic configuration of a muscle tonus measuring apparatus according to an embodiment of the present invention that measures muscle tonus characteristics through flexion and extension movements of a patient's elbow joint.
- This muscle tonus measuring apparatus includes a detection unit 10, an arithmetic device 50 that performs arithmetic processing on measurement data, and an output device 52 that outputs an arithmetic result.
- the detection unit 10 includes a base 11 that has a substantially U-shape or a substantially U-shape and can be regarded as a substantially rigid body. As shown in FIG. 1, the detection unit 10 is attached so as to sandwich the wrist joint of the subject 1, and the examiner 2 flexes and extends the elbow joint of the subject 1 through the detection unit 10.
- a pair of force sensors 20a and 20b are fixed to a pair of sandwiching plates 12a and 12b of the base 11 facing each other so as to face each other.
- the force sensors 20a and 20b there is no limitation on the structure as long as the compressive force applied to the force sensors 20a and 20b can be detected, and conventionally known general-purpose force sensors can be used. If the direction in which the pair of force sensors 20a and 20b face each other is the Z axis, the force sensors 20a and 20b detect at least a force in the Z axis direction.
- the force sensors 20a and 20b for example, general-purpose triaxial small force sensors that detect forces in the triaxial direction including the Z axis can be used.
- the direction of the force applied to the subject 1 by the examiner 2 can be corrected, or the detected Z-axis direction Force data can be corrected.
- the opposing surfaces of the force sensors 20a and 20b (the hands of the subject 1) A flexible pad may be affixed to the surface abutting the joint portion.
- a gyro sensor 30 is fixed to the bridging plate 13 that connects the pair of sandwiching plates 12a and 12b of the base 11.
- the gyro sensor 30 detects a change in posture of the detection unit 10 including the gyro sensor 30 that changes in accordance with the flexion and extension motion of the elbow joint of the subject 1.
- the muscle tonus measuring apparatus of the present embodiment further includes surface electrodes 40a and 40b for detecting surface myoelectric potential.
- the surface electrodes 40a and 40b are attached to the positions of the biceps brachii muscle and the triceps brachii muscle of the subject 1, respectively.
- known electrodes used for measuring surface myoelectric potential can be used.
- the detection unit 10 moves along an arc centered on the elbow joint.
- the posture of the detection unit 10 is maintained so that the Z axis is always parallel to the tangential direction of the arc.
- the force sensors 20a and 20b output a voltage corresponding to the force in the Z-axis direction that the examiner 2 applies to the subject 1 when the examiner 2 performs flexion and extension movement of the elbow joint of the subject 1.
- the voltages output from the force sensors 20 a and 20 b are amplified by the force sensor amplifier 21 as necessary, and then input to the arithmetic unit 50 via the A / D conversion board 51.
- the voltage according to the change in the posture output from the gyro sensor 30 is input to the arithmetic device 50 via the A / D conversion board 51.
- the voltages output from the surface electrodes 40 a and 40 b are amplified by the electromyogram amplifier 41 as necessary, and then input to the arithmetic unit 50 via the A / D conversion board 51.
- FIG. 2 is a diagram showing a data analysis technique performed by the arithmetic device 50 in the muscle tonus measuring apparatus according to the present embodiment.
- the joint torque is the force in the Z-axis direction detected via the force sensors 20a and 20b and the distance between the elbow joint of the subject 1 and the mounting position of the detection unit 10 measured separately (that is, during the flexion and extension movement).
- the radius of the arc in which the detection unit 10 moves is calculated.
- the joint angle is calculated by integrating the posture change (angular velocity) of the detection unit 10 detected via the gyro sensor 30. Then, the temporal change (raw waveform) of the joint torque and the joint angle is separated into the above four phases, and the muscle tonus characteristics from the relationship between the joint angle and the joint torque in each of the dynamic flexion phase and the dynamic extension phase. Extract the amount.
- the muscle tonus characteristic amount include a joint dynamic flexion phase spring coefficient, a joint dynamic extension phase spring coefficient, a sum of bias differences (details will be described later), and the like.
- the temporal change (raw waveform) of the surface myoelectric potential detected through the surface electrodes 40a and 40b is separated into the above four phases, and the myoelectric activity feature amount is extracted.
- the myoelectric activity feature amount include an IEMG ratio (details will be described later).
- the joint torque feature quantity may be extracted by frequency analysis of the temporal change of the joint torque in the dynamic extension phase and / or the dynamic flexion phase.
- Data regarding the above-described muscle tonus feature value, myoelectric activity feature value, and joint torque feature value obtained by the calculation device 50 may be accumulated in the calculation device 50.
- the arithmetic unit 50 may analyze the accumulated data using, for example, a statistical method to determine the severity of muscle tonus.
- the raw waveform diagram of the joint angle, joint torque, and surface myoelectric potential, the above-described various feature amounts, and the severity determination result are output to the output device 52 according to the request of the examiner.
- arithmetic unit 50 for example, a general-purpose personal computer can be used.
- the output device 52 for example, various displays and printers can be used.
- the device for measuring muscle tonus is capable of performing quantification of muscle tonus by a method that is almost as close as possible to a medical procedure that has been performed by a doctor in daily medical examinations. It is a periodical system.
- the bending and extension movement is divided into two dynamic phases that perform continuous bending and extension, and two static phases in the maximum bending position and the maximum extension position, and a characteristic amount is determined from each phase.
- the method of extracting has never been seen in the world.
- the muscle tonus measuring apparatus including the surface electrodes 40a and 40b is shown, but the surface electrodes 40a and 40b can be omitted in the present invention.
- the muscle tonus feature amount obtained from the relationship between the joint angle and the joint torque in each of the dynamic flexion phase and the dynamic extension phase the muscle stiffness of the Parkinson's disease patient The severity can be objectively identified.
- detecting the surface myoelectric potential using the surface electrode it is possible to objectively distinguish between a healthy person (UPDRS is 0) and a Parkinson's disease patient (UPDRS is 1 or more) in which muscle rigidity is recognized. It is also possible to objectively identify the severity of muscle stiffness in Parkinson's disease patients.
- the elbow joint is subjected to a sinusoidal flexion and extension motion of 1 Hz or less, and the motion system around the elbow joint is a time-invariant linear system.
- the mechanical impedance which is the vector sum of the elbow joint elasticity (spring coefficient) and viscosity, is calculated.
- the dynamics of the dynamic system is not actually the same in the dynamic flexion phase and the dynamic extension phase. In the conventional method described above, overlooking this point is considered to be the biggest cause of the dissociation between the obtained data and the clinical evaluation.
- the dynamic flexion phase and the dynamic extension phase are considered as different motion systems, and a plurality of feature quantities (muscles including a spring coefficient are determined from the relationship between the joint angle and the joint torque in each. (Tonus feature).
- Tonus feature a feature amount about the myoelectric activity in the static maximum extension phase and the maximum flexion phase.
- Patent Document 1 and Non-Patent Document 1 described above the force applied when the subject's joint is bent and extended is detected via a pressure pad filled with air (or fluid). With this method, the force detection response is poor.
- a force sensor is used. Since the force sensor generally has good responsiveness, the joint torque can be measured with high accuracy in real time. In addition, since the force sensor is generally small and light, it is possible to reduce the burden of mounting the detection unit 10 on the subject.
- the shape of the base on which the force sensors 20a and 20b and the gyro sensor 30 are mounted does not need to be substantially U-shaped or substantially U-shaped as in the above-described embodiment. It may be an elliptical shape or various polygonal shapes including a quadrangle, and may be an annular body having a through center. Furthermore, the base may have a movable part, or a part or the whole of the base may have flexibility for the purpose of improving the wearability to the subject.
- one force sensor that detects the pushing / pulling force applied when the examiner 2 flexes and extends the elbow joint of the subject 1 may be used.
- a stage for mounting the subject's joint may be provided, and a distance sensor for automatically measuring the distance between the stage and the detection unit 10 may be further provided. Thereby, the rotation radius of the detection part 10 required when calculating a joint torque can be measured easily.
- the gyro sensor 30 for measuring the joint angle is mounted on the base 11 together with the force sensors 20a and 20b. Thereby, the whole apparatus can be reduced in size, and joint torque and joint angle can be measured simultaneously only by mounting
- the joint angle measurement method is not limited to this, and a known angle change measurement method can be used.
- a sensor for example, a potentiometer or a rotary encoder
- the arithmetic unit that performs a predetermined calculation using the measured data and the display device that displays the calculation result may be downsized and mounted on the detection unit 10.
- the measuring device of the present invention can be applied to joints other than the elbow joint.
- the shape of the detection unit 10, the attachment location of the surface electrode, and the like can be changed as appropriate.
- the subject is relaxed in a resting position, and the examiner supports the subject's elbow joint with one hand and holds the subject's wrist joint with the other hand via the detection unit 10 to dynamically pass the subject's elbow joint.
- Performed flexion and extension exercises The measurement was started from the maximum extension position, and a repeating unit consisting of resting for 3 seconds at the maximum extension position, bending for 2 seconds, resting for 3 seconds at the maximum bending position, and extension for 2 seconds was repeated for 60 seconds. This measurement was performed twice for each subject on the left and right upper limbs to confirm reproducibility, and one data for each left and right (total of two data) was obtained for each subject.
- FIG. 3A, FIG. 4A, FIG. 5A, and FIG. 6A show raw waveform diagrams of typical measurement results of healthy subjects and Parkinson's disease patients (UPDRS 1 to 3).
- FIG. 3B, FIG. 4B, FIG. 5B, and FIG. 6B show the angle-torque characteristic diagrams in the dynamic flexion phase and the dynamic extension phase, which are obtained from these raw waveform diagrams.
- Bias difference sum In the angle-torque characteristic diagram, the average value of the torque of all the flexion phases at one joint angle was defined as the bias of the dynamic flexion phase.
- the dynamic extension phase bias was defined similarly.
- the difference between the dynamic flexion phase bias and the dynamic extension phase bias was defined as the bias difference.
- Bias differences were calculated for three joint angles of 30 °, 60 °, and 90 °, and the sum of them was defined as the sum of bias differences.
- the surface electromyogram waveforms of the maximum flexion phase (when the maximum flexion position was stationary) and the maximum extension phase (when the maximum extension position was stationary) were rectified and smoothed using a 2.5 Hz low-pass filter. Next, an integrated value (Integrated EMG IEMG) for one second of the rectified and smoothed electromyogram waveform was calculated.
- the IEMG ratio is a feature amount indicating the strength of myoelectric activity in a state where the muscle is passively extended.
- the IEMG ratio was determined for each of the biceps and triceps.
- FIG. 7A to 7E show the dynamic extension phase spring coefficient, the dynamic flexion phase spring coefficient, the sum of the bias differences, the IEMG ratio of the biceps brachii, and the IEMG ratio of the triceps brachii extracted from the 89 data. It is a box-and-whisker diagram classified and shown for each.
- the correlation coefficient r with UPDRS is 0.65 (95% CI (confidence intervals): 0.51 to 0.75) and 0.60 (95%).
- FIG. 8 is a box and whisker plot showing IEMG ratios for the biceps brachii, classified into a healthy subject group and a Parkinson's disease (PD) patient group.
- the IEMG ratio for biceps is less than 1.1 for 31 of the 39 data for healthy subjects, while 1.1 or greater for 46 of the 50 data for Parkinson's disease patients. Yes, it was considered that patients with Parkinson's disease had strong muscle tone.
- the IEMG ratio for the biceps brachii muscle had a sensitivity of 92% and a specificity of 80% when the cut-off value was 1.1, which was considered useful for distinguishing healthy subjects from Parkinson's disease patients.
- FIG. 9 shows, in order from the top, torque differential values obtained by time-differentiating elbow joint torque in the dynamic extension phase for healthy subjects, Parkinson's disease patients (without tremor), and Parkinson's disease patients (with tremor). It is the figure which showed a time-dependent change.
- a low amplitude torque differential value of about 8 Hz was observed, and in Parkinson's disease patients without tremor, an irregular amplitude torque differential value of about 6 Hz was observed.
- Parkinson's disease patients with tremor a high-amplitude torque differential value of about 4 Hz was observed.
- the frequency of gross tremor of a patient with Parkinson's disease with tremor is about 4 Hz, which is considered to be extracted.
- the peak frequency of the joint torque can be extracted as the joint torque feature amount, and using this, the discrimination between the healthy person and the PD patient and the presence or absence of the tremor of the PD patient can be performed. It was thought that identification could be performed objectively.
- the spring coefficient was obtained from the slope of the regression line in the angle range of 10 ° to 110 ° in the angle-torque characteristic diagram.
- the joint range of motion differs for each subject, and it may be considered that it is not appropriate to obtain the spring coefficient from the slope of the regression line in this joint angle range.
- the spring coefficient may be estimated from the frequency characteristics of the angle-torque system. The inventors of the present invention have confirmed that the spring coefficient calculated by this method is almost equivalent to the spring coefficient calculated from the angle-torque characteristic diagram.
- the elbow joint torque in the dynamic extension phase is time-differentiated, but the joint torque feature quantity similar to that in FIG. 9 can be extracted even if the elbow joint torque in the dynamic flexion phase is time-differentiated. It has been confirmed that this can be used to objectively identify healthy individuals and PD patients and whether or not PD patients have tremors.
- the field of use of the present invention is not particularly limited, but can be widely used, for example, for determining the severity of Parkinson's disease and for determining the therapeutic effect before and after administration of an anti-Parkinson's disease drug.
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Abstract
Description
角度-トルク特性図において、全施行の屈曲相の全データポイントのうち関節角度が10°~110°の範囲を抽出し、その回帰直線を求めた。そして回帰直線の傾きを動的屈曲相のバネ係数と定義した。動的伸展相のバネ係数も同様に定義した。
角度-トルク特性図において、ある一つの関節角度における屈曲相の全施行のトルクの平均値を動的屈曲相のバイアスと定義した。動的伸展相のバイアスも同様に定義した。動的屈曲相のバイアスと動的伸展相のバイアスとの差をバイアス差と定義した。30°、60°、90°の3つの関節角度についてバイアス差を計算し、それらの和をバイアス差の和と定義した。
最大屈曲相(最大屈曲位静止時)と最大伸展相(最大伸展位静止時)のそれぞれの表面筋電図波形を2.5Hzのローパスフィルターを用いて整流平滑化した。次いで、整流平滑化した筋電図波形の1秒間における積分値(Integrated EMG=IEMG)を計算した。上腕二頭筋のIEMG比を、(上腕二頭筋のIEMG比)=(最大伸展相におけるIEMG)/(最大屈曲相におけるIEMG)と定義した。上腕三頭筋のIEMG比を、(上腕三頭筋のIEMG比)=(最大屈曲相におけるIEMG)/(最大伸展相におけるIEMG)と定義した。IEMG比は、筋が受動的に伸展された状態での筋電活動の強さを示す特徴量である。上腕二頭筋及び上腕三頭筋のそれぞれについて、IEMG比を求めた。
11 ベース
12a,12b 挟持板
13 架橋板
20a,20b 力覚センサ
21 力覚センサ用アンプ
30 ジャイロセンサ
40a,40b 表面電極
41 筋電図用アンプ
50 演算装置
51 A/D変換ボード
52 出力装置
Claims (7)
- 被験者の関節を屈曲伸展運動させるために加えられる力を検出する少なくとも1つの力覚センサと、被験者の関節の関節角度を測定するためのセンサとを備え、
前記力覚センサで検出した力から関節を屈曲伸展させるための関節トルクを算出し、
被験者の関節を屈曲伸展運動させたときの前記関節トルク及び前記関節角度の経時的変化を、最大伸展位静止相、動的屈曲相、最大屈曲位静止相、及び、動的伸展相に分離し、
前記動的屈曲相及び前記動的伸展相の少なくとも一方における前記関節角度と前記関節トルクとの関係から筋トーヌス特徴量を抽出することを特徴とする筋トーヌス計測装置。 - 前記筋トーヌス特徴量が、関節のバネ係数を含む請求項1に記載の筋トーヌス計測装置。
- 前記バネ係数が、前記動的屈曲相及び前記動的伸展相におけるバネ係数である請求項2に記載の筋トーヌス計測装置。
- 前記筋トーヌス特徴量が、前記動的屈曲相における前記関節角度と前記関節トルクとの関係と、前記動的伸展相における前記関節角度と前記関節トルクとの関係との差に基づく特徴量を含む請求項1~3のいずれかに記載の筋トーヌス計測装置。
- 表面筋電位を測定する表面電極を更に備え、前記最大屈曲位静止相及び前記最大伸展位静止相における前記表面筋電位から筋電活動特徴量を更に抽出する請求項1~4のいずれかに記載の筋トーヌス計測装置。
- 前記関節トルクを周波数解析することにより関節トルク特徴量を更に抽出する請求項1~5のいずれかに記載の筋トーヌス計測装置。
- 前記関節が肘関節である請求項1~6のいずれかに記載の筋トーヌス計測装置。
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CN2009801231528A CN102065766B (zh) | 2008-06-20 | 2009-06-10 | 肌紧张测量装置 |
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US20110087128A1 (en) | 2011-04-14 |
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