JP5006060B2 - Transesophageal probe and ultrasonic diagnostic apparatus including the same - Google Patents

Description

  The present invention relates to a transesophageal probe and an ultrasonic diagnostic apparatus including the transesophageal probe, and more particularly to a transesophageal probe for observing the heart through an esophageal wall.

  The transesophageal probe is a probe used for diagnosing the heart by transmitting and receiving ultrasonic waves through the subject's esophageal wall. When the diagnosis of the heart is performed using an ultrasonic diagnostic apparatus equipped with a transesophageal probe, the distance from the transducer to the heart is shortened, making it less likely to be affected by tissues that interfere with ultrasonic propagation such as the ribs and lungs. Therefore, a more detailed image can be obtained when a transesophageal probe is used than when an ultrasonic image of the heart is formed by placing the ultrasonic probe for the body surface on the chest.

  Cited Document 1 describes an ultrasonic probe in which a deformable body capable of measuring pressure is added to the contact surface with the body surface. The ultrasonic probe described in the cited document 1 is for the body surface.

JP 2005-66041 A

  As described above, by using a transesophageal probe and an ultrasonic diagnostic apparatus equipped with the probe, it is possible to image the form of the heart and observe its movement. When examining the function of the heart in more detail, in addition to image diagnosis based on an ultrasonic image, there may be a case where measurement relating to heart beat such as heart rate measurement and blood pressure measurement is performed. In other words, when examining the cardiac function in detail, the cardiac function is diagnosed by comprehensively referring to the ultrasound image and the measurement results obtained by a measuring instrument other than the ultrasound diagnostic apparatus. Yes. In particular, since the transesophageal probe is used close to the heart, it is desired to obtain some additional measurement information useful for diagnosis by making use of the approach to the diagnosis target. Conventional transesophageal probes have been used for ultrasound imaging and have not been performed to obtain additional measurement information.

  An object of the present invention is to provide a transesophageal probe or an ultrasonic diagnostic apparatus capable of obtaining other measurement information in addition to measurement information obtained by transmitting and receiving ultrasonic waves.

  The present invention relates to a measurement unit that is inserted into the esophagus of a living body and has a transducer that transmits and receives ultrasonic waves to the front heart via the esophageal wall, and a positioning mechanism that makes the contact surface of the measurement unit contact the esophageal wall And pressure detecting means for detecting a pressing force applied from the esophageal wall to the contact surface in order to detect a pulsating component of the heart.

  According to the above configuration, in addition to the original function of the transesophageal probe for transmitting and receiving ultrasound to the heart, a function for detecting the pressing force applied to the contact surface can be added. The resulting pulsation component can be detected. Since the pulsation component can be detected at a position close to the heart, pressure information that is difficult to measure on the body surface can be acquired.

  Preferably, the pressure detection means includes a plurality of pressure detectors arranged around the vibrator, and a plurality of pressure detection values detected by the plurality of pressure detectors when detecting the pulsation component. It is used.

  According to the said structure, the some pressure value according to the state by which a measurement part is contact | abutted to an esophageal wall is detected by a some pressure detector. Even when it is difficult to accurately detect the pressure with only one pressure detector, the state where the pressure is applied can be monitored in detail or in a multifaceted manner by using a plurality of pressure detectors.

  Preferably, the pressure detecting means includes the medium containing chamber having the abutting surface and containing the medium therein, and a pressure sensor for detecting the pressure of the medium put in the medium containing chamber, The contact surface is formed of a flexible member that is provided in front of the vibrator and swells forward.

  According to the above configuration, the contact surface is provided in front of the vibrator so as to detect a pressing force applied over a wide range from the direction in front of the vibrator. Since the medium is stored inside the contact surface, even if a pressing force is applied to a part of the contact surface, the pressing force is transmitted by the medium and can be detected by the pressure sensor. . Since the contact surface is made of a flexible member that swells forward, it can be deformed according to the shape of the inner wall of the esophagus.

  Preferably, the measurement unit includes a guide unit that guides the movable unit that accommodates the vibrator and has the contact surface so as to be movable back and forth, and a biasing unit that biases the movable unit forward. The pressure detecting means is a pressure sensor for detecting a pressing force applied to the movable part.

  According to the above configuration, the movable part configured by integrating the vibrator and the contact surface detects the pulsating component applied to the contact surface in accordance with the back and forth movement caused by the pressing force. Can do.

  The present invention relates to a measurement unit that is inserted into the esophagus of a living body and has a transducer that transmits and receives ultrasonic waves to the front heart via the esophageal wall, and a positioning mechanism that makes the contact surface of the measurement unit contact the esophageal wall And motion detection means for detecting motion of the measurement unit caused by the heart beat in order to detect the heart beat component.

  According to the above configuration, since the motion of the measurement unit can be detected by the motion detection means, in addition to the function of the original transesophageal probe that transmits and receives ultrasound to the heart, the motion that occurs with the heart beat is detected. Can be detected. Examples of the detected motion include angular velocity, acceleration, and displacement.

  The present invention is an ultrasonic diagnostic apparatus having a transesophageal probe, wherein the transesophageal probe is inserted into a living body's esophagus and has a transducer that transmits and receives ultrasonic waves to the front heart via the esophageal wall. And a positioning mechanism for bringing the contact surface of the measurement unit into contact with the esophageal wall, a pressing force applied to the contact surface from the esophageal wall, or movement of the measurement unit caused by the pulsation of the heart And a signal processing unit for detecting a pulsation component of the heart based on a detection result of the detection unit.

  ADVANTAGE OF THE INVENTION According to this invention, both the ultrasonic image obtained by transmitting / receiving an ultrasonic wave to the heart and the pulsation component of the heart detected in a signal processing part are detectable.

  As described above, according to the present invention, in addition to the measurement information obtained by transmitting and receiving ultrasonic waves, other measurement information can be obtained.

  DESCRIPTION OF EXEMPLARY EMBODIMENTS Hereinafter, preferred embodiments of the invention will be described with reference to the drawings.

  FIG. 1 illustrates a use example of a transesophageal probe 50 according to the present invention. When the transesophageal probe 50 is used as shown in FIG. 1, the operator of the transesophageal probe 50 inserts the distal end portion 20 into the esophagus 10 through the mouth with respect to the subject 8 lying down, and the distal end portion 20. The insertion tube 18 is fed so that can reach a position close to the heart 12. After inserting the distal end portion 20 to a position close to the heart 12, the operator rotates the insertion tube 18 to direct the ultrasonic wave transmitting / receiving surface side of the distal end portion 20 in the direction in which the heart 12 exists. Thereafter, the operator operates the knob 16 of the operation unit 14 while viewing the ultrasonic tomographic image displayed on the display screen of the ultrasonic diagnostic apparatus. The operator operates the knob 16 to adjust the bending angle of the joint portion 22 while bringing the contact surface of the distal end portion 20 into close contact with the esophageal wall. By bringing the contact surface into close contact with each other, a propagation path for transmitting and receiving ultrasonic waves is ensured, and a clear ultrasonic image can be displayed in the ultrasonic diagnostic apparatus. The operator adjusts appropriately so that a tomographic image of a desired part of the heart can be clearly seen while viewing the ultrasonic image. The operation procedure of the transesophageal probe 50 according to the present invention described above is the same as the operation procedure of the conventional transesophageal probe.

  FIG. 2 is a view showing a state in which the distal end portion 20 of the transesophageal probe 50 is closely attached to the esophageal wall. Since the esophagus 10 passes through a position very close to the heart 12, when the distal end portion 20 of the transesophageal probe 50 is brought into contact with the esophageal wall, the pulsation of the heart is transmitted to the distal end portion 20 through the esophageal wall. In the embodiment of the present invention, a structure capable of detecting a heart beat component at the same time while forming an ultrasonic image of the heart is provided. This will be described in order below.

  FIG. 3 shows a block diagram of an ultrasonic diagnostic apparatus according to the present invention. The ultrasonic diagnostic apparatus shown in FIG. 3 is roughly divided into a transesophageal probe 50 and an ultrasonic diagnostic apparatus main body 60. The transesophageal probe 50 includes a distal end portion 42 that is small enough to be inserted into the esophagus, the insertion tube 18 that bends flexibly, and a long and narrow operation portion 14 formed of a hard resin. In the present embodiment, the distal end portion 42 corresponds to a measurement unit, and the distal end portion 42 includes the vibrator 30 and the detection unit 40. The insertion tube 18 has a joint portion 22 near the distal end portion 42. The operation unit 14 has a knob (see FIG. 1) for adjusting the bending angle of the joint unit 22.

  The transducer 30 built in the distal end portion 42 has an ultrasonic wave transmission / reception surface. A contact surface 28 that is in contact with the esophageal wall is disposed in a direction in which ultrasonic waves are transmitted from the transmission / reception surface. Here, the vibrator 30 may be an array vibrator in which strip-shaped vibration elements are arranged in one direction, or a two-dimensional array vibrator in which vibration elements are arranged in a matrix. The transducer 30 is electrically connected to a transmission / reception unit 62 provided in the ultrasonic diagnostic apparatus main body 60 via a bundled cable laid in the insertion tube 18.

  The detection unit 40 built in the distal end portion 42 acquires measurement information obtained by bringing the distal end portion 42 into contact with the esophageal wall. As the detection unit 40, for example, pressure detection means or motion detection means is used in the present embodiment. Of course, the pressure detecting means may be used as the motion detecting means. When using, for example, a pressure detection unit as the detection unit 40, it is desirable that the portion for detecting the pressure is a part of the contact surface 28. The detection unit 40 is electrically connected to a signal processing unit 68 provided in the ultrasonic diagnostic apparatus main body 60 via a bundled cable laid in the insertion tube 18.

  It is desirable that the tip portion 42 is pressed against the esophageal wall under certain conditions so that the measurement value measured by the detection unit 40 does not deteriorate in accuracy due to a change in measurement conditions. Therefore, during the measurement by the detection unit 40, the bending angle of the joint unit 22 is fixed by locking the operation of the knob of the operation unit 14. As a result, the distal end portion 42 is fixed and measurement can be performed while maintaining the measurement conditions constant.

  The control unit 64 provided in the ultrasonic diagnostic apparatus main body 60 outputs a control signal to the transmission / reception unit 62 and the echo signal processing unit 66. The transmission / reception unit 62 has a transmission beam forming function, generates a temporal delay distribution for a plurality of transmission signals, and outputs the delay distribution to the transducer 30. The transducer 30 transmits and receives ultrasonic waves and receives an echo signal from a living tissue existing ahead. The reception signal detected by the transducer 30 is subjected to phasing addition processing in the transmission / reception unit 62 and then output to the echo signal processing unit 66. The echo signal processing unit 66 processes received signals in order to form a heart tissue image, measure a blood flow velocity, or display a blood flow distribution state. The process may be, for example, a dynamic range conversion process for forming a B-mode image or an echo signal orthogonal detection process for forming a color flow Doppler image. Alternatively, frequency analysis processing for Doppler measurement may be used.

  In particular, if echo tracking processing is performed while paying attention to a tissue of a part of the heart while forming a B-mode image, velocity information of the tissue can be obtained. If calculation is performed based on the correlation between the velocity information and the amount of movement of the measurement target region, the myocardial strain rate (strain rate) or strain amount (strain) can also be obtained.

  On the other hand, the signal detected by the detection unit 40 is input to the signal processing unit 68. In the signal processing unit 68, an input signal analysis process is performed. As a result, a pulsating component of the heart, such as a pressure generated with the pulsation of the heart or a displacement accompanying the pulsation, is detected.

  As described above, the ultrasonic diagnostic apparatus according to the present embodiment has two functions, that is, a function for forming an ultrasonic image and a function for detecting a pulsating component of the heart. By using these two functions, ultrasonic image measurement and cardiac function measurement can be performed simultaneously. In the following, the structure of the tip part important for detecting the pulsation component of the heart will be described in detail.

  From this, four specific structural examples are shown regarding the front-end | tip part of a transesophageal probe. Three of the four are configuration examples using a pressure sensor, and the remaining one is a configuration example using an acceleration sensor. First, three configuration examples using a pressure sensor will be described in order.

  FIG. 4 is a diagram illustrating a first configuration example in which pressure is detected by two pressure sensors. 4A and 4B show the structure of the distal portion 70 of the transesophageal probe. FIG. 4A shows a top view and FIG. 4B shows a cross-sectional view. The exterior case 71 of the distal end portion 70 is made of resin, and the distal end shape of the exterior case 71 is rounded so as to easily pass through the throat of the human body. The abutment surface 72 that abuts the esophageal wall is generally flat so as to be in close contact with the esophageal wall over a wide area. As shown in FIG. 4A, the vibrator 74 is disposed at a substantially central position of the contact surface 72. The vibrator 74 includes a plurality of vibration elements, and a signal cable is connected to each vibration element. In the first configuration example, the vibrator 30 is housed in the fixed case 76, and the position of the vibrator 74 does not change. On both sides of the fixed case 76, two pressure detectors 78A and 78B having the same structure are arranged along the axial direction (Y-axis direction) of the insertion tube. For example, the pressure detector 78A includes a pressure sensor 80A, a cylindrical case 82A, and a raised film 84A, and a sealed space containing air is formed therein. The cylindrical case 82A is formed of a hard resin, and a pressure sensor 80A is bonded to one opening of the cylindrical case 82A. A raised film 84A swelled in a dome shape is bonded to the other opening of the cylindrical case 82A. The two raised films 84A and 84B constitute a part of the contact surface 72 as shown in FIG.

  The pressure sensor 80A is provided with a sensor chip 86A for detecting pressure at the bottom of the through hole. In this configuration example, a sensor chip 86A on which a piezoresistive element is mounted is used taking advantage of the fact that the pressure detectors 78A and 78B can be made compact. As other pressure detection means, a pressure sensitive rubber material, PVDF (polyvinylidene fluoride), a strain gauge, a semiconductor sensor having a diaphragm, or the like may be applied.

  The two pressure sensors 80A and 80B have signal cables 88A and 88B that output pressure signals converted into voltages. These signal cables 88A and 88B are respectively connected to a part of the bundled cable in the insertion tube 18, and the pressure signals output from the pressure sensors 80A and 80B are transmitted to the signal processing unit via the bundled cable. 68 (see FIG. 3). In addition, a power supply line for applying a DC constant voltage from the ultrasonic diagnostic apparatus main body 60 is also connected to the two pressure sensors 80A and 80B.

  The raised film 84A provided at a position facing the pressure sensor 80A across the cylindrical case 82A is formed of an elastically deformable resin film. The bulge surface of the film is directed in the + Z-axis direction corresponding to the ultrasonic wave transmission direction. The raised film 84A is not limited to resin, but may be formed of a flexible rubber material. The flexibility of the raised membrane 84A is such that the pressure detection voltage of the sensor chip 86A is not saturated even if a larger force is applied to the raised membrane 84A than when the contact surface 72 is pressed against the esophageal wall. The thickness is appropriately set. The outer case 71 and the insertion tube 18 are joined by an adhesive so that liquid or the like does not enter the outer case 71. In the insertion tube 18, an indirect portion for bending the distal end portion 70 in the vertical and horizontal directions and a bundled cable for transmitting an electric signal are laid.

  When the heart is diagnosed, the joint portion is bent by operating the knob 16 of the operation unit 14 at a position close to the heart in the esophagus, and the contact surface 72 is brought into close contact with the esophageal wall. When the contact surface 72 is pressed against the esophageal wall, the two raised films 84A and 84B are slightly depressed and deformed. In this state, the pressing force changes with strength as the heart beats, so that the two raised films 84A and 84B are also deformed with the change of the pressing force. The air enclosed in the pressure detectors 78A and 78B causes stress to the sensor chips 86A and 86B as the raised films 84A and 84B change. Since the electrical resistance of the piezoresistive element increases in response to an increase in stress applied to the sensor chips 86A and 86B, the stress is converted into a voltage signal in the sensor chips 86A and 86B.

  The pressure signals from the two pressure sensors 80A and 80B are separately transmitted to the signal processing unit 68 via a bundled cable in the insertion tube. In the signal processing unit 68, two pressure signals are analyzed. In performing the analysis, the two pressure signals may be individually processed, or the two pressure signals may be averaged. As a signal analysis method, for example, an analysis process for obtaining a difference between the maximum value and the minimum value of the voltage signal and corresponding to the difference in the pressing force caused by the pulsation of the heart can be cited. In this example of the analysis method, the maximum value and the minimum value of the voltage signal correspond to the pressing force applied to the contact surface 72, and the difference between the maximum value and the minimum value of the voltage signal corresponds to the pulsation component of the heart.

As described above, according to the distal end portion 70 as the first configuration example, the pressure sensors 80A and 80B are added, so that the pulsation component of the heart can be measured in real time together with the formation of the ultrasound image of the heart. However, the measurement of the pulsation component of the heart may be performed while the ultrasonic image formation is performed or the measurement time is shifted back and forth. In addition, a member that elastically deforms is used for the dome-shaped raised membranes 84A and 84B, and the pressure is detected by directly contacting the esophagus wall, so that a local site inside the human body that cannot be measured from the body surface Pressure information can be obtained. In addition, by inserting a transesophageal probe into the subject's esophagus, it is possible to perform ultrasonic imaging of the heart and measurement of the pulsating component of the heart. Therefore, the burden on the subject can be reduced. In addition, since the two pressure detectors 78A and 78B are provided, two independent pressure signals corresponding to the degree of close contact with the esophageal wall can be detected. Furthermore, two pressure detectors 78A, since the arrangement before and after the vibrator 74 along the extension length direction of the insertion tube 18 to 78B, the width direction of the front end portion (X axis direction) and thickness direction (Z axis direction) A small tip can be maintained without increasing the dimensions. That is, it is possible to provide a compact transesophageal probe that places little burden on the subject when inserted into the subject's esophagus.

  Next, a second configuration example will be described with reference to FIG. In the second configuration example, the pressure can be detected from a wide range using the contact surface of the tip. 5A and 5B show the structure of the distal end portion 90 of the transesophageal probe according to the second configuration example. FIG. 5A is a top view and FIG. A cross-sectional view is shown. In particular, the structure of the contact surface 92 and the pressure detection medium are different from those of the tip portion which is the first configuration example described above with reference to FIG. The contact surface 92 includes a flexible resin film 96 projecting forward of the vibrator 94. The material of the film 96 may be a silicon material or a rubber material in addition to the resin. The film 96 is provided wider than the area of the transmission / reception surface of the vibrator 94 as shown in the top view of FIG. The membrane 96 is disposed in front of the vibrator 94, fills the interior with a liquid, and functions as a chamber for storing a pressure transmission medium. Incidentally, it is preferable that the liquid to be filled is a liquid such as water or oil that has little hindrance to ultrasonic wave propagation. The liquid inside the membrane 96 is enclosed in a sealed space constituted by the membrane 96 and a pressure sensor 98 for liquid. Only one liquid pressure sensor 98 is provided in the tip portion, and a diaphragm is provided in the inside thereof. The pressure sensor 98 converts the stress generated in the diaphragm by the pressure of the liquid into a voltage signal and outputs the voltage signal. The voltage signal of the pressure sensor 98 is output to the signal cable 100 and transmitted to the signal processing unit 68 via the bundled cable.

  The second configuration example is a multi-plane method capable of forming an infinite number of tomographic scan planes. The vibrator 94 is accommodated in a cylindrical pulley 102. The pulley 102 is rotatable around a central axis parallel to the Z axis, and a wire 104 extending from the scanning unit is hung on the pulley 102. The pulley 102 housing the vibrator 94 rotates at a fixed position with respect to the contact surface 92 by pulling the wire 104. That is, in this configuration example, the vibrator 94 can be rotated clockwise or counterclockwise using the wire 104.

  The operation of the second configuration example will be described. The operation of the operation unit performed when the heart is diagnosed is the same as in the first configuration example, and the contact surface 92 is brought into close contact with the esophageal wall by bending a joint (not shown). Since the area on the front side of the membrane 96, that is, the area occupied in the contact surface 92, is larger than the total area of the two raised membranes 84A and 84B shown in the first configuration example, the membrane 96 has a wide surface to the esophagus. In close contact. The shape of the film 96 is deformed according to the degree of adhesion. The internal pressure of the membrane 96 is output as a voltage signal from the pressure sensor 98. Similar to the first configuration example, the output voltage signal is transmitted to the signal processing unit 68 via the bundled cable, and signal analysis is performed.

  As described above, according to the second configuration example, since the area of the film 96 protruding on the contact surface 92 can be increased, the detection range of the pressing force can be expanded. Therefore, it is possible to monitor the pressing force applied not only to the local portion of the esophageal wall but also to the entire distal end portion 90. Further, since the liquid is used as a pressure transmission medium, the volume change of the medium is smaller than that of the gas, and the pressing force can be transmitted to the pressure sensor 98 with high accuracy. In the second configuration example, the multi-plane method is adopted. However, a bi-plane method in which two tomographic scan planes can be obtained vertically and horizontally, or an infinite number of tomographic scan planes can be provided without providing a rotation mechanism. A scanning method using the obtained 2D array may be used.

  Next, a third configuration example will be described with reference to FIG. In the third configuration example, the pressure applied to the contact surface 112 can be directly detected. 6 (A) and 6 (B) show the structure of the distal end portion 110 of the transesophageal probe according to the third configuration example, FIG. 6 (A) is a top view, and FIG. 6 (B) is the top view. A cross-sectional view is shown. The vibrator 114 shown in FIG. 6B is fixed inside the fixed case 116. In front of the fixed case 116, an acoustic lens 118 made of silicon rubber is bonded and provided. The acoustic lens 118, which is a part of the contact surface 112, has a shape projecting forward. The vibrator 114, the fixed case 116, and the acoustic lens 118 constitute a movable part 106 as an integral unit. The movable portion 106 is provided with two slide grooves 120A and 120B as guide means for sliding the movable portion 106 back and forth on the side surface side. Further, two suspension portions 122A and 122B as urging means are provided behind the movable portion 106. The two suspension parts 122A and 122B have the same mechanism, and the suspension parts 122A and 122B have springs 124A and 124B and pressure sensors 126A and 126B, respectively. The springs 124A and 124B are provided between the back surface of the fixed case 116 and the pressure sensors 126A and 126B. The two springs 124A and 124B urge the movable portion 106 forward by elastic force with the two pressure sensors 126A and 126B as fulcrums. Therefore, a gap is generated between the pressure detection surfaces 127A and 127B of the two pressure sensors 126A and 126B and the back surface of the fixed case 116. The voltage signals of the pressure sensors 126A and 126B are output to the respective signal cables 128A and 128B. The pressure signals detected by the two pressure sensors 126A and 126B are transmitted to the signal processing unit 68 independently of each other.

  The operation of the third configuration example will be described. In order to bring the abutting surface 112 into close contact with the esophageal wall, the bending of a joint (not shown) is used as in the case of the first configuration example. When a pressing force is applied to the abutting surface 112, a force for contracting the two springs is applied via components (such as the acoustic lens 118, the vibrator 114, and the fixed case 116) constituting the movable portion 106. When the pressing force applied to the bulged surface of the acoustic lens 118 exceeds the urging forces of the two springs, the movable unit 106 moves backward along the slide grooves 120A and 120B. When the spring contracts and the back surface of the fixed case 116 comes into close contact with the two pressure sensors 126A and 126B and the gap in front of the pressure detection surfaces 127A and 127B is lost, the pressure sensors 126A and 126B detect the pressure signal. The pressure sensors 126A and 126B convert the detected pressure signal into a voltage signal and output it to a signal cable. That is, the two springs 124A and 124B have an offset function of a pressure detection level for obtaining a pressure signal only when a pressing force exceeding the elastic force of the spring is applied. In other words, the two springs have a selection function of detecting only a pressing force of a certain level or higher without detecting a weak pressing force as a pressure signal.

  As described above, according to the third configuration example, the transducer 114, the fixed case 116, and the acoustic lens 118 are integrally structured. Therefore, the ultrasonic transmission path until the transducer 114 transmits the ultrasonic wave to the esophageal wall is provided. It can always be kept constant. Therefore, the effect of the acoustic lens 118 is always constant when transmitting ultrasonic waves. Further, since a threshold is provided for the pressure detection level by the spring, only a pressing force of a certain level or higher can be detected without detecting a weak pressing force as a pressure signal. Further, since the pressing force is directly transmitted to the pressure sensors 126A and 126B through the movable portion 106 as a solid without using gas or liquid as a pressure transmission medium, the change in the pressing force is sensitively sensitive. Can be detected well.

  Next, as a fourth configuration example, a description will be given of a configuration example in which an acceleration sensor is applied to obtain the amount of displacement of the distal end portion associated with the pulsation of the heart. As long as the acceleration sensor used in this configuration example is small enough to be mounted on the tip, sensors of various detection methods can be used. In particular, a one-chip semiconductor acceleration sensor that outputs a large voltage gradually as the tilt angle from the vertical direction increases with the vertical direction as a reference direction is suitable. Since the dimensions of the semiconductor acceleration sensor itself are as small as several millimeters square, the acceleration sensor is built in the tip. When one or two acceleration sensors having such characteristics are used, the inclination degree with respect to each of the three orthogonal XYZ axes can be converted into a voltage signal and output. The voltage signal output from the acceleration sensor is transmitted to the signal processing unit 68 via the signal cable as in the case of the other configuration examples described above. The signal processing unit 68 detects each inclination angle in the three-axis directions by monitoring the voltage signal output from the acceleration sensor. By constantly monitoring and analyzing each inclination angle, the angular velocity, acceleration, and displacement amount of the tip portion where the acceleration sensor is mounted can be obtained. Therefore, the signal processing unit 68 grasps the movement (angular velocity, acceleration, displacement amount) of the distal end that is in contact with the esophageal wall. The signal processing unit 68 analyzes the movement of the distal end and performs a process of removing a relatively slow movement component associated with respiration, etc., and extracts a movement component associated with the heartbeat.

  As described above, in the transesophageal probe, for example, by using an acceleration sensor as the motion detection means, the ultrasonic diagnosis of the heart and the pressure accompanying the pulsation of the heart can be simultaneously measured. If an acceleration sensor is used, a force component balanced in a static state is not detected, so that only a dynamic momentum can be extracted. Furthermore, if an acceleration sensor is used, not only a simple motion such as a reciprocating motion but also a motion that draws a twisting trajectory in the pulsating component of the heart is extracted and discriminated. can do. Incidentally, the acceleration sensor is not only used alone, but may be shared with the pressure sensor. That is, the pressure detection means described above as the first, second, and third configuration examples may be further added to the transesophageal probe that includes the acceleration sensor as the motion detection means that is the fourth configuration example.

  In addition, although the example of a structure which mounts a pressure sensor or an acceleration sensor with respect to a transesophageal probe until now is shown, it is a pressure sensor or an acceleration sensor with respect to other ultrasonic probes (for example, a transvertebral probe, a transvaginal probe, etc.) Can also be installed.

  As described above, according to the transesophageal probe and the ultrasonic diagnostic apparatus including the same according to the present invention, measurement information useful for diagnosing the heart is obtained in addition to measurement information obtained by transmitting and receiving ultrasonic waves. be able to.

It is a figure which shows the usage example of the transesophageal probe which concerns on this invention. It is a figure which shows the state which stuck the front-end | tip part of the transesophageal probe to the esophageal wall. 1 is a block diagram of an ultrasonic vibration device according to the present invention. It is a figure which shows the front-end | tip part of the transesophageal probe which concerns on the 1st Embodiment of this invention. It is a figure which shows the front-end | tip part of the transesophageal probe which concerns on the 2nd Embodiment of this invention. It is a figure which shows the front-end | tip part of the transesophageal probe which concerns on the 3rd Embodiment of this invention.

Explanation of symbols

  8 Subject, 10 Esophageal, 12 Heart, 14 Operation part, 16 Knob, 18 Insertion tube, 20, 42, 70, 90, 110 Tip part, 22 Joint part, 24 Scanning plane, 28, 72, 92, 112 Contact surface, 30, 74, 94, 114 transducer, 40 detection unit, 50 transesophageal probe, 60 ultrasonic diagnostic apparatus body, 62 transmission / reception unit, 64 control unit, 66 echo signal processing unit, 68 signal processing unit, 71 exterior Case, 76, 116 Fixed case, 78A, 78B Pressure detector, 80A, 80B Pressure sensor, 82A, 82B Cylindrical case, 84A, 84B Raised membrane, 86A, 86B Sensor chip, 96 membrane, 98 Pressure sensor, 102 Pulley, 104 Wire, 106 Movable part, 118 Acoustic lens.

Claims (6)

Provided in the insertion tube to be inserted into the esophagus of a living body, a measuring unit having a transducer for transmitting and receiving ultrasonic waves in front of the heart via the esophageal wall,
A positioning mechanism for abutting the abutment surface of the measuring unit against the esophageal wall;
Pressure detecting means for detecting a pressing force applied from the esophageal wall to the contact surface in order to detect the pulsating component of the heart;
Only including,
The transesophageal probe is characterized in that the pressure detection means includes two pressure detectors provided before and after the vibrator in the extending direction of the insertion tube . The transesophageal probe according to claim 1,
The transesophageal probe, wherein each pressure detector swells in a dome shape on the esophageal wall side . A measurement unit that is inserted into the esophagus of a living body and has a vibrator that transmits and receives ultrasound to the heart in front through the esophagus wall
A positioning mechanism for abutting the abutment surface of the measuring unit against the esophageal wall;
Pressure detecting means for detecting a pressing force applied from the esophageal wall to the contact surface in order to detect the pulsating component of the heart;
Including
The pressure detecting means includes
A medium accommodating chamber having the abutting surface and having a medium contained therein;
A pressure sensor for detecting the pressure of the medium placed in the medium storage chamber;
With
The transesophageal probe is characterized in that the abutment surface is formed of a flexible member that is provided in front of the transducer and is swelled forward. A measurement unit that is inserted into the esophagus of a living body and has a vibrator that transmits and receives ultrasound to the heart in front through the esophageal wall;
A positioning mechanism for abutting the abutment surface of the measuring unit against the esophageal wall;
Pressure detecting means for detecting a pressing force applied from the esophageal wall to the contact surface in order to detect the pulsating component of the heart;
Including
The measuring unit is
Guiding means for accommodating the vibrator and guiding the movable part having the contact surface so as to move back and forth;
Biasing means for biasing the movable part forward;
Have
The transesophageal probe characterized in that the pressure detecting means is a pressure sensor for detecting a pressing force applied to the movable part. A measurement unit that is inserted into the esophagus of a living body and has a vibrator that transmits and receives ultrasound to the heart in front through the esophagus wall
A positioning mechanism for abutting the abutment surface of the measuring unit against the esophageal wall;
Motion detecting means for detecting the motion of the measuring unit caused by the heart beat in order to detect the heart beat component;
Only including,
The transesophageal probe characterized in that the motion detection means is an acceleration sensor, and a dynamic amount of motion is detected for the measurement unit by the acceleration sensor . An ultrasound diagnostic apparatus having a transesophageal probe,
The transesophageal probe is
A measurement unit that is inserted into the esophagus of a living body and has a vibrator that transmits and receives ultrasound to the heart in front through the esophageal wall;
A positioning mechanism for abutting the abutment surface of the measuring unit against the esophageal wall;
A detecting means for detecting a pressing force applied to the contact surface from the esophageal wall, or a movement of the measuring unit caused by the pulsation of the heart;
Have
Furthermore, the signal processing unit is provided we are detecting a beat component of the heart based on a detection result of said detecting means,
The ultrasonic diagnostic apparatus, wherein the signal processing unit detects a pulsation component of the heart by excluding a motion component due to respiration from a detection result of the detection means .

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