JPH0347100B2 - - Google Patents

Description

DETAILED DESCRIPTION OF THE INVENTION The present invention relates to a pressure reaction force measuring device for detecting the state of soft tissue of a living body, for example, the soft and hard state of muscles, as a pressure reaction force, and determining whether the tissue is abnormal or normal. It is.

It is well known that in a living body, for example, a human body, the degree of fatigue, disease state, or abnormality can be perceived depending on the hardness or tension of soft tissues such as muscles and internal organs. Among these, a more familiar symptom is muscle stiffness.
This stiffness, as everyone has experienced, feels heavy and tense, and when it gets worse, it can even be painful, and when you touch it, you can feel the muscles being stiff and tense. The former is a subjective symptom, and the latter is one of objective findings.
However, in any case, these results are determined based on the subjective scale of sensation, and each patient's
The scale differs depending on each doctor and is not constant. If the degree of stiffness can be evaluated using an appropriate objective scale and expressed numerically, the degree of stiffness will not only contribute to diagnosis but also be useful for determining therapeutic effects and testing drugs. Become.

In order to serve this purpose, conventional methods have been attempted that mainly measure muscle stiffness, as described below. An example of such a device is shown in FIG.
This device applies an external force to the soft tissues of the body to be measured, such as muscles, and causes the tissues to dent, thereby displaying the soft and hard state of the tissues as numerical values of the external forces, and detecting the presence or absence of abnormalities or their degree. It is something to do.

In the figure, 1 is a movable indenter for pressing on the soft tissue to be measured, its tip 1a is the part that presses the surface of the soft tissue, and the other end is not shown, but it is always in use. It is spring-biased in the projecting direction and is connected, for example, to a rack that meshes with a pinion. When the movable indenter 1 is retracted into the external force display section 2, the pinion is rotated and the pointer 3 integrated with the pinion is configured to rotate. Reference numeral 4 denotes two guide legs fixed to the external force display section 2 with fixing members 5, which are provided at laterally symmetrical positions with a predetermined interval apart with the movable indenter 1 as the center. The tip end 1a of the movable indenter 1 is connected to the leg ends 4a and 4b of the guide legs 4, 4 in the state before measurement.
It is set to protrude by a predetermined amount from the line connecting the lines.

To explain the operation of the conventional device having such a configuration, the distal end 1a of the movable indenter 1 is brought into contact with the epidermis 6a of the soft tissue 6 and an external force is applied to the leg end of the guide leg 4 as shown in FIG. 4a and 4b are the epidermis 6
Press until it touches point a. At this time, the movable indenter 1 receives a reaction force from the soft tissue 6 and is retracted against the spring biasing force in the external force display section 2, and the pointer 3 rotates to generate the value of the external force corresponding to the reaction force. Display.

This conventional device is used to measure muscle tension before and after exercise. For example, it compares the measured value before and after exercise at the same measurement point to measure the degree of muscle fatigue. was.

However, the conventional device described above cannot measure thick muscles, soft tissues deep under the epidermis, etc. because the pressurizing distance is narrow.

Further, in this device, the tip portion 1a of the movable indenter 1 is small and gets stuck in the tissue, making it impossible to measure external force or causing pain to the subject. Conventionally, measurements have been made while accepting such problems, but the pathological condition of stiffness involves extremely complex factors, and as in the conventional example mentioned above, it has been difficult to measure muscle stiffness in an engineering way. There has been some controversy over the measurement of In other words, in clinical practice, muscle stiffness is merely a secondary effect of stiffness, and subjective symptoms such as heaviness and pain reported by patients are more important factors. The nature of the stiffness that causes these subjective symptoms is not fully understood. However, stiffness refers to muscle function, surrogate system,
If we consider that the feedback system, which is comprised of the nervous system, which includes the central nervous system via the circulatory system and spinal reflex system, is in a vicious cycle due to various causes, pain and muscle stiffness can be attributed to modulation of this system. It can be considered as a thing. From this standpoint, it is expected that muscle stiffness will probabilistically match subjective symptoms, and it can be treated as an objective measure of the degree of stiffness.

However, this measure is insufficient to be considered absolute. This is because there are large individual differences and it is difficult to keep measurement conditions constant.

On the other hand, Japanese Patent Laid-Open Publication No. 138456/1983 discloses a pine surge machine equipped with a function for determining pine surge effects.

That is, in this pine surge machine, an acceleration sensor and a pressure sensor are installed on a vibration table that is excited by a vibrator to vibrate the human tissue, and the stiffness of the mechanical impedance of the human tissue is obtained from the outputs of the acceleration sensor and the pressure sensor. The system is configured to detect the stiffness and compare it with the initial stiffness value input into the memory to determine the pine surge effect.

However, as in the latter conventional example, when vibrations or high frequencies are applied to the soft tissue of a living body using a vibrator, a reaction occurs within the soft tissue, disturbing the internal mechanism and changing the initial state. The problem is that it becomes impossible to understand.

In addition, in this latter conventional example, it is difficult to correlate the output value of the device with the case of palpation, and it is difficult to measure the pressure reaction force of thick muscles or soft tissues deep under the epidermis. is also difficult.

The present invention has been made in view of the above-mentioned conventional problems, and its purpose is to measure the pressure reaction force from the soft tissue of a living body under a constant external force, thereby determining the state of the soft tissue. , provides a pressure reaction force measurement device for soft tissue of a living body that can diagnose with an accuracy comparable to palpation by an experienced doctor, and can also measure pressure reaction force of soft tissue in areas that were previously considered impossible. It's about doing.

In order to achieve the above object, the present invention provides a pressure reaction force measuring device that measures the reaction force from the soft tissue of a living body to be measured by pressing on the soft tissue and grasps the state of the soft tissue. , a thick-walled cylindrical portion, a thin-walled diaphragm formed to close one end surface of the thick-walled cylindrical portion and having approximately the same size as the pad surface of a human finger, and a non-pressure-receiving surface of the diaphragm. and a strain gauge attached to the side, one end surface of the thick-walled cylindrical part and the diaphragm are in contact with the soft tissue, and an external force is applied from the non-pressure-receiving surface side via the thick-walled cylindrical part. pressure detection means for converting and detecting the pressure on the soft tissue when the pressure is applied to the soft tissue into an electrical signal corresponding to the pressure using the strain gauge; and a sensing section for detecting the external force, which receives the external force. external force detecting means for converting and detecting an external force when the external force is transmitted to the thick-walled cylindrical portion of the pressure detecting means through an external force transmitting member into an electric signal corresponding to the external force, Under a constant external force applied to the pressure detection means based on the output corresponding to the external force detected by the external force detection means, the pressure detection means detects pressure reactions of various soft tissues of the living body. This device is characterized by being configured to be able to measure force.

Hereinafter, the present invention will be explained in detail based on examples.

FIG. 2 is a sectional view of a pressure reaction force measuring device showing the configuration of an embodiment of the present invention. In the figure, reference numeral 7 denotes a sensing section constituting an external force detection means for detecting an external force that presses the epidermis 6a of the soft tissue 6. The sensing portion 7 includes a diaphragm 8 that is displaced in response to the external force, and one surface (non-pressure receiving surface) of the diaphragm 8.
The strain gauge 9 is attached to the diaphragm 8 and detects the displacement of the diaphragm 8 as a change in resistance value and converts it into an electrical quantity. The sensing part 7 is fixed to the top wall of a case 10, which has a hollow cylindrical shape in the figure, with the pressure receiving surface of the diaphragm 8 facing downward, and a pressing member 11 is attached to the center of the diaphragm 8 from below. Abutting or connecting. An opening 10a is provided in the lower part of the case 10, and a transmission rod 12 as an external force transmission member is inserted from below so as to be slidable in the axial direction. Inside the case 10, a spring 13 is disposed between the transmission rod 12 and the pressing member 11.
is inserted. Among the transmission rods 12, case 1
A sensing section 14 as a pressure detection means for detecting the pressure on the soft tissue 6 is disposed at the tip of the side protruding from 0.
is fixed. The sensing portion 14 is formed to close one end surface (lower end surface in FIG. 2) of the thick-walled cylindrical portion, and has a size approximately the same as the ventral surface of a human finger (for example, a thumb) (for example, 6 to 8 mm). ) and this diaphragm 1.
A strain gauge 16 is attached to the non-pressure-receiving surface (the surface opposite to the surface abutting the soft tissue) of 5. The pressure reaction force on the soft tissue when one end surface of the thick-walled cylindrical portion and the diaphragm 15 are in contact with the soft tissue of the living body and an external force is applied from the non-pressure-receiving surface side through the thick-walled cylindrical portion. , the pressure reaction force is converted into an electric signal corresponding to the pressure reaction force and detected by the strain gauge 16.

When measuring the pressure reaction force using the above-described embodiment configured in this way, after the sensing part 14 is brought into contact with the epidermis 6a of the soft tissue 6, the case 10 is gripped, etc. Apply an external force to Then, the sensing portion 14 receives a reaction force from the soft tissue 6, so the transmission rod 12 receiving the reaction force is retracted into the case 10, and the pressing member 11 deflects the diaphragm 8 via the spring 13. As a result, the resistance value of the strain gauge 9 attached to the diaphragm 8 changes, and an amount of electricity corresponding to the external force is extracted. The diaphragm 15 of the sensing portion 14 that is in contact with the epidermis 6a of the soft tissue 6 receives a pressure reaction force from the soft tissue 6, and an amount of electricity corresponding to this pressure reaction force is extracted.

FIG. 3 is a system block diagram for receiving, displaying, and recording outputs from the sensing sections 7 and 14 of FIG. 2. In the figure, the output corresponding to the external force from the sensing section 7 is displayed on the external force display 18 of the display section 17 as an external force value. Further, the output corresponding to the pressure from the sensing section 14 is displayed on the pressure reaction force display 19 of the display section 17 as a pressure value in the soft tissue 6. The external force values and pressure reaction force values displayed on the external force display 18 and the pressure reaction force table 19 are simultaneously recorded by a recorder 20 such as an oscillograph. This display and recording may be digital or analog.

FIGS. 4a and 4b show recorded waveform diagrams of external force and pressure reaction force recorded by the recorder 20. FIG. Figure a
shows the pressure reaction force at several points on the same muscle, assuming a constant external force. If the level values indicated by the broken lines in Figure a are taken as normal values, it will be possible to detect abnormalities at measurement points P2 and P3.
Figure b shows the pressure reaction force on the same measurement point when the external force is 1Kg, 2Kg, and 3Kg.
In Figure b, it is confirmed that the pressure reaction force varies depending on the magnitude of the external force. Since the magnitude of the pressure reaction force at this time varies depending on the depth of the soft tissue 6 from the epidermis 6a, the thickness of the soft tissue 6, etc., it is desirable to set the external force appropriately according to each.

According to the embodiment configured in this way, the external force and the pressure reaction force from the soft tissue due to the external force are displayed or recorded at the same time, so that the pressure reaction force under the predetermined external force can always be measured. I can do it. Therefore, if the pressure reaction force of the soft tissue under normal conditions is known, even when measured by different operators,
It is possible to always judge whether or not the soft tissue is normal based on the same standard, and it is also possible to evaluate it using an appropriate objective scale without incorporating the subjectivity of the measurer.

Furthermore, even soft tissues with different configurations can be easily measured. For example, the pressure reaction force of muscles in a tissue composed of skin (including fat) - muscle - bone, the pressure reaction force of muscle in a tissue composed of skin - muscle, and the pressure reaction force of muscle in a tissue composed of skin - muscle - internal organs. Each muscle or visceral pressure reaction force has its own unique pressure reaction force, and by knowing in advance the standard value of pressure reaction force corresponding to these in normal tissues, it is possible to determine whether or not it is abnormal. It becomes possible to judge. This also allows individual differences to be ignored.

Furthermore, for example, when measuring the pressure reaction force of a soft tissue 6 located deep from the epidermis 6a, such as an internal organ, the external force can be increased.

Furthermore, since the diameter of the diaphragm 15 of the sensing section 14 is made the same size as the surface of a human finger pad, it becomes easier to correlate the output value of this device with the value obtained by palpation. In this way, in this embodiment, it is possible to measure pressure reaction forces of various tissues.

Note that the present invention is not limited to the embodiments described above, and various modifications can be made without departing from the gist of the present invention.

For example, as shown in FIG. 5a, a flange-like portion 21 may be formed at the tip of the transmission rod 12, and when configured in this way, the pressure reaction force of the affected area can be measured more accurately. At the same time, it is possible to prevent the distal end from being inserted into the tissue and causing an erroneous measurement of external force. Next, as shown in FIG. 2B, a cap-shaped portion 23 is formed so that the tip of the cap is along the eyeball 22, and the sensing portion 14 is configured to measure the fundus pressure (the pressure of the fundus blood vessels). You can also do that. Although not shown, by configuring the tip of the transmission rod to smoothly roll or slide along the epidermis of soft tissue, it is possible to check for liver cirrhosis in internal organs, such as the liver, and to check for cirrhosis in muscles, such as muscle movement. It becomes possible to continuously check the system.

Furthermore, as a method of measuring the measured value, when the external force that is the output value of the sensing section 7 reaches a predetermined value, a measurement command signal is issued from a control circuit (not shown), and the output value from the sensing section 14 is determined. By sampling and storing the pressure reaction force of soft tissue, the pressure reaction force at a predetermined external force can be easily displayed or recorded even when external force is continuously applied.
This may be a case where the pressure reaction force against a plurality of external forces such as 1 kg, 2 kg, and 3 kg, for example, is measured.

As described in detail above, according to the present invention, by measuring the pressure reaction force from the soft tissue of a living body under the application of a constant external force, it is possible to determine the initial state before movement or the state of the soft tissue after movement. However, it can be diagnosed with an accuracy comparable to that of palpation by a skilled doctor, and it is also possible to measure pressure reaction force in soft tissues, etc. deep beneath the epidermis of thick muscles, which was previously considered impossible, by region. At the same time, since the method measures pressure reaction force statically, unlike the conventional method of determining the pine surge effect while applying electrical vibrations or high frequencies, a reaction occurs inside the muscle, making it difficult to grasp the initial state. Furthermore, since the size of the diaphragm of the pressure detection means that comes into contact with the soft tissue of the living body is approximately the same size as the surface of a human finger pad, this device can be used both by palpation and by this device. It is possible to provide a device for measuring pressure reaction force in the soft tissue of a living body, which makes it easy to correlate with the output value, allows the degree of stiffness to be evaluated using an objective scale, and does not cause pain to the subject. .

[Brief explanation of drawings]

FIG. 1 is a front view showing an example of the configuration of a conventional device mainly for measuring pressure reaction force of muscles, FIG. 2 is a sectional view showing the configuration of an embodiment of the present invention, and FIG.
System block diagram for displaying and recording measured values according to the same embodiment, Figures 4a and b
5 is a waveform diagram showing output waveforms of external force and pressure reaction force in the same embodiment, and FIGS. 5a and 5b are partial sectional views in another embodiment of the present invention. 1... Moving indenter, 2... External force display section, 4... Guide leg, 6... Soft tissue, 7, 14... Sensing section,
8, 15...Diaphragm, 9, 16...Strain gauge, 11...Press member, 12...Transmission rod, 1
3...Spring.

Claims (1)

[Scope of Claims] 1. A pressure reaction force measurement device that measures a reaction force from a soft tissue of a living body to be measured and grasps the state of the soft tissue by pressing the soft tissue, comprising: a thick-walled cylinder; a thin-walled diaphragm formed to close one end face of the thick-walled cylindrical part and having approximately the same size as the belly surface of a human finger; and a strain gauge attached to the non-pressure-receiving surface side of the diaphragm. Therefore, the soft tissue when one end surface of the thick-walled cylindrical portion and the diaphragm are in contact with the soft tissue and an external force is applied from the non-pressure-receiving surface side via the thick-walled cylindrical portion. pressure detecting means for detecting the above pressure by converting it into an electric signal corresponding to the pressure by the strain gauge; and a sensing section for detecting the external force, and the external force is received by the external force and transmitted through the external force transmitting member. External force detection means for converting the external force transmitted to the thick-walled cylindrical portion of the pressure detection means into an electric signal corresponding to the external force and detecting the external force, and detecting the external force by the external force detection means. The pressure detection means is capable of measuring pressure reaction forces of various soft tissues of a living body under a constant external force applied to the pressure detection means based on an output corresponding to the external force applied to the pressure detection means. 1. A pressure reaction force measuring device for soft tissue of a living body, characterized in that: