JP6372915B2 - Fat diagnosis device and fat diagnosis accessory device - Google Patents

Description

  The present invention relates to a fat diagnostic device and a fat diagnostic accessory device for performing a fat diagnosis by measuring a change in ultrasonic velocity before and after heating on a measurement site of a subject. More specifically, the present invention relates to a fat diagnostic device and a fat diagnostic accessory device that can be attached to a commercially available ultrasonic diagnostic device capable of image diagnosis, and enables fat diagnosis based on an ultrasonic velocity change as a retrofit function or an optional function. . The present invention is used, for example, in the diagnosis of fatty liver and the diagnosis of fat (fibrous or lipidic) nature of intravascular plaques such as the carotid artery.

  In order to diagnose visceral fat, which is one of the risk factors for lifestyle-related diseases, as a new diagnostic imaging method that uses changes in the ultrasonic velocity before and after heating, the region of interest is heated by light irradiation and heated. Proposed a detection method and detection device for adipose tissue that measures the change in ultrasonic velocity before and after temperature, detects the region where the ultrasonic velocity changes negatively with respect to temperature change as adipose tissue, and diagnoses fat distribution (See Patent Document 1).

  A fat diagnostic apparatus (adipose tissue detection apparatus) described in Patent Document 1 will be described. This apparatus has an apparatus main body equipped with a control unit necessary for acquiring a B-mode tomographic image and an ultrasonic velocity change image, and a probe that directly contacts the body surface of the subject to perform ultrasonic irradiation and heating. It has. The probe is a linear array probe that irradiates the measurement area of the subject with ultrasonic waves, and a near-infrared light irradiation for heating the measurement area of the subject next to the linear array probe. A dedicated probe in which the infrared laser light source for performing the above is arranged side by side so as to be directed toward the same measurement region is used.

  The linear array probe has a large number of transducers composed of linearly arranged piezoelectric elements, and each transducer transmits an ultrasonic signal with a pulse wave excited by a drive signal from a control unit. And receiving an ultrasonic echo signal from within the subject in response to the ultrasonic signal. Then, scanning is performed by sequentially switching transducers that perform transmission and reception according to a control signal. The infrared laser light source is adapted to irradiate near infrared light of 700 nm to 1000 nm from the side of the linear array probe.

Next, the operation of measuring the ultrasonic velocity change and measuring the fat with this apparatus will be described. A measurement region in the subject is specified in advance by image diagnosis using a B-mode image or the like. The specified measurement area is heated by irradiating near infrared light from an infrared laser light source, and after a predetermined heating time has elapsed, the linear array probe is driven to sequentially scan pulsed ultrasonic signals. In this manner, the ultrasonic waves are transmitted sequentially, and ultrasonic echo signals that are received signals from the subject are sequentially received. And the waveform of the ultrasonic echo signal (reception signal) acquired in the light irradiation state is stored as the ultrasonic echo signal after light irradiation.
After storing the received waveform of the ultrasonic echo signal after the light irradiation, the light irradiation is stopped. When a predetermined time elapses after the irradiation is stopped and the temperature of the subject is sufficiently lowered, the linear array probe is driven again to transmit an ultrasonic signal and receive an ultrasonic echo signal from the subject. . And the waveform of the ultrasonic echo signal (reception signal) acquired in the light irradiation stop state is stored as a non-irradiation ultrasonic echo signal. The stored ultrasonic echo signal is displayed as a B-mode tomographic image by displaying its amplitude in luminance.
Subsequently, the ultrasonic velocity change is obtained from the relationship shown below based on the ultrasonic echo signals after the light irradiation and at the time of non-irradiation.

FIG. 12 is a schematic diagram showing an ultrasonic echo signal during non-irradiation (before heating) and an ultrasonic echo signal after light irradiation (after heating) in a certain partial section. The ultrasonic velocity at the time of non-irradiation is V, and the ultrasonic velocity after light irradiation is V ′. Also, let τ be a pulse interval that occurs when an ultrasonic signal propagates between certain boundaries during non-irradiation, and let τ−Δτ be a pulse interval that occurs when an ultrasonic signal propagates after light irradiation between the same boundaries (constant distance) And That is, it is assumed that the pulse interval is shifted by Δτ due to a temperature change so as to be shortened.
At this time,
V · τ = V ′ · (τ−Δτ) (1)
Therefore, the ultrasonic velocity change data can be calculated by the following equation (2) from the time change of the pulse interval between the two echo signals.
V ′ / V = τ / (τ−Δτ) (2)
Accordingly, the pulse interval (τ) and the waveform shift amount (Δτ) in the region of interest are calculated from the two measured echo signals, and the change in the ultrasonic velocity at each part (the ultrasonic velocity change ratio) is calculated based on the equation (2). (V ′ / V)) is calculated.

Subsequently, based on the calculated ultrasonic velocity change ratio (V ′ / V) of each region, a region where this value is smaller than 1 (region where the ultrasonic velocity change with respect to heating is negative) is determined as a fat region. .
That is, the ultrasonic velocity propagating in water and fat is 1524 m / sec in water and 1412 m / sec in fat when the temperature is 37 ° C. When the ultrasonic velocity change with respect to temperature change is compared, it is as follows. is there.
Water: +2 m / sec / ° C
Fat: -4 m / sec / ° C
Therefore, when the temperature rises in muscles and internal organs (liver etc.) that contain a lot of water, the ultrasonic velocity increases in the fat part, and the polarity of the ultrasonic velocity change is reversed. To do.
Therefore, a fat region can be detected by specifying a region where the ultrasonic velocity change is negative when the temperature of the measurement region is changed.

  Then, based on the analysis result of the ultrasonic velocity change by multiple ultrasonic echo signals acquired by scanning the multi-channel array probe, the two-dimensional distribution of the ultrasonic velocity change is imaged and displayed on the display device. By doing so, the fat region is clearly displayed separately from other parts.

JP 2010-005271 A

  In the fat diagnostic apparatus described in Patent Document 1, the measurement region is heated with light, and the fat region is imaged by obtaining the ultrasonic velocity change by the ultrasonic echo signal before and after the heating. Yes.

  However, when the fat diagnosis of a living body is performed by light heating, there is a limit to the depth from the body surface that can be heated. That is, infrared laser light (near infrared light) can only be sufficiently heated from the body surface by about 3 cm to 4 cm due to the influence of strong light absorption in the living body. On the other hand, there is a liver (fatty liver) as one of measurement sites for which fat diagnosis is required. Since the liver is located in the deep part of the living body of about 5 cm to 10 cm from the body surface, it is difficult to perform stable light heating and high-precision measurement cannot be performed.

Therefore, another heating means is required to enable heating up to the deep part of the living body. In that case, it is possible to use ultrasonic energy as a heating source. That is, the ultrasonic wave can reach a deep position of 5 cm to 10 cm from the body surface by selecting a frequency band of 1 MHz to 3 MHz (referred to as a low frequency ultrasonic region). Can be warmed.
Therefore, it is conceivable to warm the liver by irradiating ultrasonic waves in a low frequency ultrasonic region using a commercially available ultrasonic diagnostic apparatus for image diagnosis and a multi-channel array probe for image diagnosis as they are.

  However, the ultrasonic pulse signal for diagnosis used in a general-purpose ultrasonic diagnostic apparatus for image diagnosis may be a weak output signal, but the ultrasonic wave for heating has a relatively large output within a range where there is no safety problem. It is necessary to irradiate with power. Moreover, in order to maintain the living body in a warmed state, it is necessary to continue irradiation with the output power necessary for warming.

  Therefore, since the output power of ultrasonic waves used for image diagnosis and heating is greatly different, a commercially available ultrasonic diagnostic apparatus for image diagnosis and a probe for image diagnosis are used as they are for heating (and fat diagnosis). If you try to use it for the same purpose, problems will occur.

In other words, in order to be able to carry out everything from diagnostic imaging to warming and fat diagnosis using a commercially available ultrasound diagnostic device, not only adding an ultrasound source for heating in the ultrasound diagnostic device. As for the probe, it is possible to irradiate the measurement site with high output power with the multi-channel array-type probe, and for diagnostic imaging and heating that has been modified to have a durable probe structure. Significant modifications such as making an integrated probe are required.
However, the multi-channel array type probe has a structure in which a large number (for example, 128) of piezoelectric elements (vibrators) are arranged in a line on the irradiation surface of a predetermined width of the probe. One piezoelectric element must be thin, and it is difficult to form a multi-channel probe having sufficient durability even when used at a high output.

There is also a problem from a practical aspect such as cost. It has been explained that it is necessary to use a low-frequency ultrasonic region (1 MHz to 3 MHz) in order to make the ultrasonic wave reach the deep part of the living body. However, in order to obtain a clear image, it is preferable to employ an ultrasonic wave having a resolution as high as possible, and it is necessary to increase the frequency of the ultrasonic wave as much as possible. In a commercially available ultrasound for diagnostic imaging, there is also an apparatus that obtains a clear image by irradiating a measurement region with an ultrasonic pulse wave of about 3 MHz to 10 MHz (referred to as a high frequency ultrasonic region).
Therefore, in order to be able to perform fat diagnosis in the deep part of the living body and image diagnosis using a clear image, a wide band from a low-frequency ultrasonic region to a high-frequency ultrasonic region (for example, 1 MHz to 10 MHz), and larger than before. An ultrasonic diagnostic apparatus using a high-performance probe that can be used with output power must be used, which not only makes the manufacture of the probe difficult, but also increases the manufacturing cost.

  On the other hand, it is also conceivable to heat by ultrasonic irradiation from a position different from the diagnostic imaging probe. Specifically, instead of the infrared laser light source in the fat diagnostic apparatus described in Patent Document 1 described above, it is also conceivable to arrange an ultrasonic heating source side by side on the diagnostic imaging probe. However, in this case, the traveling direction of the ultrasonic wave emitted from the diagnostic imaging probe and the traveling direction of the heating ultrasonic wave are not parallel. It is difficult to make them coincide with each other, and misalignment is likely to occur.

  In addition, there will be a safety problem. In other words, the liver is located inside the ribs, but bone tissue such as ribs absorbs ultrasonic waves strongly. Therefore, when heating with ultrasonic waves, the bone tissue (ribs) is not irradiated to the liver. Irradiation is necessary. If an irradiation surface for ultrasonic heating is placed at a position different from the irradiation surface of the diagnostic imaging probe, the area irradiated with ultrasonic waves inevitably increases near the body surface, and the ribs are also irradiated. This method is difficult to adopt from the viewpoint of safety.

From the above, the present invention firstly provides a commercially available diagnostic ultrasound for diagnostic imaging by attaching it as a retrofit function or optional function to a commercially available diagnostic ultrasound apparatus for diagnostic imaging without any major modification. A fat diagnostic apparatus and fat which enables image diagnosis using an apparatus and an array type probe for image diagnosis as before, and enables fat diagnosis by warming a living body and measuring ultrasonic velocity change An object is to provide a diagnostic accessory.
In addition, secondly, with respect to the measurement position determined in the image diagnosis, the direction of travel of the ultrasound for image diagnosis and the direction of travel of the ultrasound for heating are irradiated in a coaxial direction in parallel. It is an object of the present invention to provide a fat diagnostic apparatus and a fat diagnostic accessory apparatus capable of performing fat diagnosis at exactly the same measurement position.
A third object of the present invention is to provide a fat diagnostic device and a fat diagnostic accessory that can safely perform a fat diagnosis of a liver (fatty liver) located in the deep part of a living body.

In connection with the subject of this invention, the characteristic of the fatty liver used as one of the diagnostic objects was examined. In fatty liver, fat is present as individual lipid droplets in individual cells, and such cells are generally distributed uniformly. Therefore, in fat diagnosis of fatty liver, if the echo signals before and after heating (echo signals in an area sufficiently wider than the cell level) of one channel (one measurement point) are measured, information on fat from multiple cells (super It was found that fatty liver can be measured with a small number of channels (including 1 channel). Therefore, it has been found that a fat diagnosis in which it is determined whether or not it is fatty liver by comparing with a preset reference value does not necessarily require a two-dimensional image display.
On the other hand, in the diagnosis of localized fatty liver and multiple localized fatty liver, diagnosis of intravascular plaque such as carotid artery (fibrous or lipid), etc., it is necessary to diagnose the distribution of fat, and it is a multi-channel Detailed and useful information can be obtained by performing diagnosis by displaying an image of a two-dimensional fat distribution using an array type probe.
The present invention has been made on the basis of such knowledge, and a fat diagnostic device that performs fat diagnosis without displaying an image of fat distribution, and a fat that performs fat diagnosis by displaying an image of fat distribution. Invented a diagnostic accessory.

That is, the fat diagnostic apparatus of the present invention, which has been made to solve the above problems, acquires an echo signal from a measurement site using a multi-channel main probe, and performs an image diagnosis using an ultrasonic image formed by the echo signal. A fat diagnostic apparatus attached to an ultrasonic diagnostic apparatus for performing a fat diagnosis by calculating an ultrasonic velocity change from echo signals of a measurement site before and after heating, wherein the fat diagnostic apparatus includes an ultrasonic wave for heating The sub-probe capable of irradiation and the ultrasonic wave generated by the ultrasonic wave source for heating are applied to the measurement site via the sub-probe to control the heating, and the pulse is transmitted via the sub-probe. A fat measurement control unit that performs control to transmit echo signals and measure echo signals before and after heating; a fat information calculation unit that calculates fat information including ultrasonic velocity changes from the echo signals before and after heating; Wherein the lobes and the secondary probe is mounted at the same time, the common exit port is provided for emitting ultrasonic waves emitted from the probe to the measurement site, and a probe holder for selectively transmitting and receiving either one of the ultrasonic A common standoff filled with a fluid ultrasonic propagation medium so as to be in contact with the transducer of each probe, and ultrasonic waves emitted from one of the probes in the standoff A switching mechanism for switching so as to guide the light to the exit is attached.

According to the present invention, two main probes and two sub-probes are attached to the probe holder at the same time, and ultrasonic waves are irradiated in a common axial direction from a position on the body surface positioned via the probe holder. . That is, ultrasonic waves to a probe holder which is irradiated from a common exit port Ri Contact provided, Ri by that the traveling direction of the ultrasonic two probes in the flop Robuhoruda is adjusted, the main probe and secondary probes The axes are made to coincide.

  In addition, a probe capable of irradiating ultrasonic waves for heating (high output) is used as the sub probe. In other words, the multi-channel probe, which is the main probe used for diagnostic imaging, has a thin piezoelectric element and has problems with durability and the like for heating that requires output power. A probe that can be used with a large output power is used. Such a warming probe can be easily formed by using, for example, a probe with a small number of channels. As the probe for heating, the number of channels is not limited as long as the measurement site can be heated, so there is no problem even if the number of channels is small. For example, the number of channels may be one or about 2 to 5 channels.

  In the present invention, fatty liver is measured without displaying an image of fat distribution. That is, image diagnosis is performed by the ultrasonic diagnostic apparatus and the main probe (multi-channel probe), and a measurement position for performing heating and fat diagnosis is determined from the displayed ultrasonic image (B-mode image). Subsequently, heating to the determined measurement position is performed via the auxiliary probe. Further, echo signal measurement before and after heating is performed through the sub probe. The echo signal measured with the secondary probe cannot form an image of fat distribution, but fatty liver fat is present in individual cells as fat droplets, and the cells containing the fat droplets are uniformly distributed. Therefore, if there is an echo signal before and after heating measured from one measurement point by one channel of such a sub-probe, the ultrasonic velocity change can be measured from it, and fatty liver A fat diagnosis can be performed.

According to the fat diagnostic apparatus of the present invention, it is not necessary to modify the existing equipment for the ultrasonic diagnostic apparatus and the main probe used for image diagnosis, and the fat diagnostic function can be provided only by retrofitting a fat diagnostic apparatus including a secondary probe. Can be added.
In addition, the main probe and the sub probe are used by being attached to the probe holder so that the axial directions of the ultrasonic waves (traveling directions of the ultrasonic waves) irradiated from the two probes by the probe holder coincide with each other. Therefore, it is possible to perform heating and fat diagnosis with the auxiliary probe at the exact same measurement position with respect to the measurement position determined by the image diagnosis with the main probe.

  Further, since the secondary probe is not used for image formation, a robust secondary probe using a small number of channels (for example, 1 channel) of piezoelectric elements (vibrators) can be formed at low cost. That is, by reducing the number of piezoelectric elements, it becomes possible to form a probe with almost no dimensional restrictions (unlike a multi-channel probe), and a heat dissipation member is provided around the piezoelectric element. It is possible to easily take measures against large outputs such as. Therefore, by using a sub-probe of a small number of channels, it becomes possible to irradiate a heating ultrasonic wave with a large output power and to have a highly durable probe. This eliminates the need for a high-performance integrated probe that can perform image diagnosis and heating with a single multi-channel probe, thereby reducing the cost of the apparatus.

  In the measurement of fatty liver, ultrasonic irradiation for image diagnosis and ultrasonic irradiation for heating can be performed through a common irradiation port, so the area irradiated with ultrasonic waves near the body surface Therefore, it is possible to perform ultrasonic heating safely while avoiding the ribs and the like.

The probe holder is a common stand in which the main probe and the sub probe are mounted simultaneously and filled with a fluid ultrasonic propagation medium (specifically, water, oil, etc.) so as to be in contact with the transducer of each probe. In addition to the formation of the off-state, a switching mechanism for switching the ultrasonic wave emitted from one of the probes to the emission port may be attached in the stand-off. Specifically, the switching mechanism can use a movable mirror, a movable shutter, or the like.
As a result, the probe to be used can be exchanged with only a simple switching operation by the switching mechanism, and the ultrasonic waves emitted from each probe are efficiently shared within the probe holder with little attenuation. It can irradiate from the irradiation port.

In the above invention, the auxiliary probe may be composed of a one-channel vibrator.
According to this, when measuring the ultrasonic velocity change for fat diagnosis, it is not necessary to scan only by transmitting and receiving a pulse ultrasonic signal from one transducer. It can be greatly simplified. In addition, since the multi-channel transducer is not scanned like the main probe, it is possible to repeatedly measure at high speed by increasing the number of times of measurement per one channel.

  In the above invention, the fat information calculation unit may output the ultrasonic velocity change or the fat information as a numerical value or character data. As a result, since the image display is not performed, the fat measurement result by the echo signal at one measurement point can be expressed numerically and expressed as a determination result of the ultrasonic velocity change or the presence or absence of fat or a fat ratio, It becomes easy to compare with a preset reference value of fatty liver by digitization.

  In the above invention, the fat measurement control unit may transmit an ultrasonic wave of 0.5 MHz to 3 MHz from a heating ultrasonic source. Thereby, it is possible to effectively heat the liver up to the deep part of the living body.

In the above invention, the fat diagnostic apparatus may be connected to an external computer device that has a display device and can perform calculation processing, and the fat information calculation unit may be provided in the external computer device.
Thereby, the calculation of the ultrasonic velocity change is performed by the external computer device, and the result of fat diagnosis such as the ultrasonic velocity change can be displayed using the display screen.

Further, the accessory device for fat diagnosis of the present invention made from another point of view,
Acquired echo signals from the measurement site using a multi-channel main probe and attached to an ultrasound diagnostic device that performs image diagnosis using the ultrasound image formed by the echo signals. A fat diagnostic accessory device for performing a fat diagnosis by calculating a change in ultrasonic velocity, wherein the fat diagnostic accessory device includes a sub-probe capable of performing ultrasonic irradiation for heating, and an ultrasonic probe for heating. A heating control unit that performs heating control by irradiating the measurement site with ultrasonic waves generated by a sound wave source through the auxiliary probe, and heating measured by using the main probe and the ultrasonic diagnostic apparatus. An echo signal transmission control unit that performs control to acquire and transmit echo signals before and after temperature from the ultrasonic diagnostic apparatus, and fat that calculates fat information including ultrasonic velocity changes from the transmitted echo signals before and after heating Affection A calculation unit, wherein said main probe and the secondary probe is mounted at the same time, the common exit port is provided for emitting ultrasonic waves emitted from the probe to the measurement site, and, optionally either ultrasound A common stand-off filled with a flowable ultrasonic wave propagation medium so as to be in contact with the transducer of each probe, and either one of the probes in the stand-off A switching mechanism for switching so that the ultrasonic wave emitted from the laser beam is guided to the emission port is attached .

According to the present invention, similar to the fat diagnostic apparatus described above, the main probe and the sub-probe are mounted on the probe holder, and from the position on the body surface positioned through the probe holder, from the common exit port. The ultrasonic waves are irradiated in the same direction. That is, the probe holder is provided with a common exit port so that the ultrasonic axes irradiated from the main probe and the sub-probe coincide with each other. Incidentally, two probes, similar to the aforementioned fat diagnostic device, to use by two was simultaneously attached to the probe holder. It is possible to replace and install one probe at a time, but in the latter case, it is necessary to replace the main probe and sub probe twice, so in the present invention, two probes are mounted simultaneously. I try to keep it.

  Further, as the sub-probe, a probe capable of ultrasonic irradiation for heating is used as in the above-described fat diagnostic apparatus. Specifically, it is possible to use a secondary probe that is formed of a robust piezoelectric element by using a small number of channels (for example, one channel) and can be used with a large output power.

  In the present invention, by displaying an image of fat distribution, fatty liver is measured or the properties of plaques in blood vessels such as the carotid artery are measured. Specifically, image diagnosis is performed with an ultrasonic diagnostic apparatus and a main probe (multi-channel probe), and a measurement position for performing heating and fat diagnosis is determined from the displayed ultrasonic image (B-mode image). Subsequently, heating is performed to the measurement position determined via the auxiliary probe. Then, echo signal measurement before and after heating is performed again via the main probe. By measuring the echo signal for fat diagnosis with the main probe, the number of echo signals necessary for the formation of ultrasound images before and after heating can be acquired. A change distribution image, and further, a fat distribution image obtained by extracting a region where the ultrasonic velocity change is negative can be formed, and fat diagnosis can be performed using the image.

1 is an external view showing a configuration of an entire fat diagnostic system provided with a fat diagnostic device according to an embodiment of the present invention. The block diagram which shows the structure of the fat diagnostic apparatus in FIG. The external view which shows the sub probe of 1 channel for heating. Sectional drawing which looked at the probe holder of FIG. 1 from the side. The flowchart which shows the measurement operation | movement procedure by the fat diagnostic system of 1st, 2nd embodiment of this invention. The external view (reference example) which shows the structure of the whole fat diagnostic system to which the fat diagnostic apparatus of other embodiment of this invention was attached. The block diagram (reference example) which shows the structure of the fat diagnostic apparatus in FIG. It is the external view which looked at the probe holder of FIG. 6 from the front, (a) shows a main probe mounting state, (b) shows a sub probe mounting state (reference example) . The external view which shows the structure of the whole fat diagnostic system to which the attachment apparatus for fat diagnostics of further another embodiment of this invention was attached. FIG. 10 is a block diagram showing the configuration of the fat diagnostic accessory apparatus in FIG. 9. The flowchart which shows the measurement operation | movement procedure by the fat diagnostic system of FIG. The schematic diagram which shows the echo signal at the time of non-irradiation (before heating) and after light irradiation (after heating).

(Embodiment 1)
Hereinafter, embodiments of the present invention will be described with reference to the drawings. Here, it demonstrates as what diagnoses a fatty liver. FIG. 1 is an external view showing a fat diagnostic system A in which a fat diagnostic apparatus 10 according to an embodiment of the present invention is attached to a commercially available ultrasonic diagnostic apparatus 1 as a retrofit. The fat diagnosis system A includes an ultrasonic diagnostic apparatus 1 for image diagnosis, a main probe 2 for image diagnosis, a control box (dedicated board) 3, a sub probe 4 used for heating and fat diagnosis, A probe holder 5 having a switching mirror 5a for switching a probe to be used and an external computer device 6 are included.

  In the present embodiment, the fat diagnosis apparatus 10 is configured by the control box 3, the sub probe 4 for fat diagnosis, the probe holder 5, and the external computer device 6.

  As the main probe 2 of the ultrasonic diagnostic apparatus 1 (commercial product), a multi-channel (for example, 128 transducers) array type probe (commercial product) used for image diagnosis is used. An ultrasonic image such as a B-mode image is displayed on the display screen of the ultrasonic diagnostic apparatus 1 by transmitting and receiving the ultrasonic signal while scanning. As the ultrasonic diagnostic apparatus 1 and the main probe 2 for image diagnosis, existing commercial products are used as they are, and they are exclusively used for searching, determining, and confirming a measurement site by an ultrasonic image.

  FIG. 2 is a block diagram showing components of the fat diagnostic apparatus 10 in the fat diagnostic system A. The control box 3 includes a high-frequency power source 21 that generates a heating ultrasonic wave (for example, a sine wave), a pulser / receiver circuit 22 that transmits a pulse wave for fat diagnosis and receives an echo signal from a living body, A switch 23 for switching whether the probe 4 is connected to the high-frequency power source 21 side or the pulsar / receiver circuit 22 side, an A / D converter 24 for converting the received echo signal into a digital signal, and a memory for storing the echo signal 25. A controller 26 is provided for performing operations such as driving of ultrasonic waves for heating and pulse waves for fat diagnosis, and switching of the switching mirror 5a and the switch 23.

The control box 3 transmits the ultrasonic wave for heating from the high-frequency power source 21 via the sub probe 4, and controls the heating of the measurement site and transmits the pulse wave by the pulser / receiver circuit 22. The echo signal is received and functions as a fat measurement control unit 11 that performs control for measuring the pre-warming echo signal and the post-warming echo signal.
Here, the measurement order of the “pre-heating echo signal” and the “post-heating echo signal” will be described. In fat measurement by ultrasonic velocity change, a temperature change is generated by heating the measurement site, and echo signals under two different temperatures, that is, before the temperature change and after the temperature change, The “echo signal” and the “hot echo signal” on the high temperature side are measured. Measurement can be performed regardless of which measurement is performed first. However, in actual measurement, heating is first performed, heating is stopped in a state where the temperature has been increased by a predetermined temperature, an “echo signal after heating” is measured immediately after the heating is stopped, and then, for a predetermined time (for example, 10 seconds). After the temperature is lowered after ˜20 seconds, the “echo signal before heating” is measured.
This is due to the following reason. When a part of a living body is heated, blood flow increases due to a physiological action to return the heated portion to a normal temperature state, and a strong cooling action is exerted. Therefore, if the echo signal is measured in the state where the blood flow has been increased first and the blood flow has increased, the “cooling echo signal after the warming” is measured immediately after the heating is stopped, As a result, the “echo signal before heating” can be measured when the temperature returns to the normal temperature state due to a rapid temperature change.

  The measured “echo signal before warming” and “echo signal after warming” are digitized by the A / D converter 24 and output to the external computer device 6 and are also stored in the memory 25 and required. It can be output at any time.

  As shown in FIG. 3, the secondary probe 4 is a cylindrical probe made up of a single-channel vibrator 4a. The vibrator 4a uses a high-power piezoelectric element capable of irradiating heating ultrasonic waves. Further, a heat radiating member is provided around the vibrator 4a. The sub probe 4 is a main probe. Compared to 2, it has a tough structure and is sufficiently radiated.

The sub-probe 4 transmits the ultrasonic wave for heating by switching operation of the switch 23 and transmits / receives the pulse wave ultrasonic signal for fat diagnosis for one line.
The echo signal for one line received by the transducer 4 a is sent to the fat measurement control unit 11 (control box 3), digitized, and sent to the external computer device 6 and the memory 25. The echo signal for one line includes a signal from each part in the depth direction at one measurement point.

  FIG. 4 is a cross-sectional view showing the structure of the probe holder 5 viewed from the side. The probe holder 5 is formed of a rectangular body having four sides surrounded by side walls 5b, and the upper surface is an opening 5c into which the main probe 2 for image diagnosis having a square horizontal section is inserted. The lower surface is an opening (emission port) 5d for emitting ultrasonic waves, and the opening 5d is closed by using a sheet 5f such as silicon rubber through which ultrasonic waves can pass. The sheet 5f is provided to fill the case with a fluid ultrasonic wave propagation body L such as water as a standoff. An opening 5e is formed on one surface of the side wall 5b, and a cylindrical sub probe 4 is attached thereto. The vibrator 2a of the main probe 2 and the vibrator 4a of the sub probe 4 are in contact with the ultrasonic wave propagation body L filled in the case.

Further, in the probe holder 5, a movable switching mirror 5a that reflects ultrasonic waves is provided in a fluid ultrasonic wave propagation body L (standoff). The switching mirror 5a is switched by an operation signal from the controller 26 so that only one of the ultrasonic wave from the main probe 2 and the ultrasonic wave from the sub probe 4 is emitted from the common opening 5d. is there.
That is, when irradiating ultrasonic waves (for image diagnosis) from the main probe 2, the switching mirror 5a moves forward of the sub probe 4 so that the ultrasonic waves from the vibrator 2a can go straight to the opening 5d. When irradiating the ultrasonic wave (for heating or fat diagnosis) from the sub-probe 4, the ultrasonic wave from the vibrator 4a is moved by moving to the position of 45 degrees obliquely with respect to the vibrator 2a and the vibrator 4a. Sound waves are reflected by the switching mirror 5a and emitted from the common opening 5d. The axial direction of the ultrasonic wave emitted from the sub probe 4 is made to coincide with one of the axial directions of the ultrasonic wave emitted from the main probe 2 (the axial direction of the ultrasonic wave emitted from the central vibrator). Yes, the irradiation position of the sub probe 4 can be grasped at the time of image diagnosis by the main probe 2.
The ultrasonic wave can be blocked by attaching an ultrasonic absorbing material such as a rubber material to the back surface of the switching mirror 5a on the side facing the transducer 2a and the inner wall part where the ultrasonic wave in the probe holder 5 is reflected. By doing so, it is not necessary to turn off the power supply on the main probe 2 side even during the irradiation of ultrasonic waves on the subprobe 4 side.

As the external computer device 6, a general-purpose personal computer device (for example, a notebook personal computer) including a CPU, a memory, an input device (keyboard or the like), and a display device (liquid crystal panel) is used, and the control box 3 (fat measurement control unit 11). ) Of the echo signal before and after heating output from) is calculated by the above-mentioned equation (2) in the partial section corresponding to the echo signal from the liver, and the ultrasonic velocity change (in this case, the ultrasonic velocity ratio) is calculated. Calculation processing is performed.
That is, the waveform shift of the echo signal before and after heating is based on the echo signal received after heating and the echo signal received before heating, using the same principle and method as the conventional example described in FIG. A quantity (Δτ) is calculated, and a process of calculating a pulse interval (τ) between tissue boundaries in the measurement region is performed. And based on Formula (2), the process which calculates the ultrasonic velocity ratio (V '/ V) of each partial area is performed.

In addition, fat determination (fat liver presence / absence determination) is performed based on the value of the ultrasonic velocity ratio, or the fat ratio is calculated from comparison with reference data stored in advance, and these are calculated as fat information. Processing is performed. Then, the ultrasonic velocity ratio value and fat information (fat determination, fat ratio) are displayed on the display device.
The output data displayed at this time is an ultrasonic velocity change ratio, a fat determination result, and a fat ratio calculation result, and these are displayed as numerical values (characters).
In this manner, the external computer device 6 functions as a fat information calculation unit 12 that calculates fat information including changes in ultrasonic velocity based on measurement results of echo signals before and after heating.

  Note that the data calculated by the external computer device 6 (fat information calculation unit 12) is one-channel data, so that B-mode images cannot be displayed. However, the ultrasonic velocity change ratio, fat determination result, fat ratio In addition to displaying numerical values (characters), the waveform of the received echo signal of one line can be displayed on the screen. Furthermore, one line of echo signals can be displayed in time series as in the M mode.

Next, a measurement procedure by the fat diagnostic system A (including the fat diagnostic apparatus 10) will be described based on the flowchart of FIG.
First, a fat measurement position is searched and determined by image diagnosis by the ultrasonic diagnostic apparatus 1 (S101). That is, the switching mirror 5a is set so that the main probe 2 side is turned on, and the ultrasonic diagnostic apparatus 1 is operated to take a B-mode image by a pulse wave of about 3 MHz, and this is displayed on the screen to perform image diagnosis. Search for a measurement position suitable for fat measurement. At this time, the search may be performed so as to obtain a clear image with higher resolution by further increasing the frequency of the pulse wave as necessary.

  Next, heating control by the control box 3 (fat measurement control unit 11) is performed on the determined measurement position (S102). That is, the controller 26 of the control box 3 is operated to switch the switching mirror 5a so that the sub probe 4 side is turned on, the switch 23 is set to the high frequency power source 21 side, the high frequency power source 21 is turned on and the sub probe 4 is turned on. The ultrasonic wave for heating is irradiated through. If the ultrasonic wave to be irradiated is 0.5 MHz to 3 MHz, the position of the liver can be efficiently heated, but the irradiation is preferably performed at about 0.7 MHz to 1 MHz. And heating is maintained until a heating area | region raises about 0.5 degreeC-2 degreeC, and is stabilized. For example, the heating time becomes stable after about 30 seconds.

  Next, the heating is stopped, and the echo signal is measured in the temperature rising state immediately after the heating is stopped (S103). That is, the controller 26 is operated to switch the switch 23 to the pulsar / receiver circuit side 22 without changing the switching mirror 5a, to transmit a pulse wave through the sub probe 4 and to wait for and receive an echo signal. . The received echo signal is stored in the memory 25 as an “echo signal after heating” and is sent to the external computer device 6 (fat information calculation unit 12).

  Next, after the measurement of the “echo signal after warming” is completed, a predetermined time set in advance as the time required to return to normal temperature is further passed (for example, after about 10 to 20 seconds have passed). The echo signal when the temperature is lowered to the normal temperature before the temperature is measured (S104). That is, while the switching mirror 5a and the switch 23 are left as they are, a pulse wave is transmitted again via the sub probe 4, and an echo signal is awaited and received. Since the received echo signal returns to the same signal as the normal temperature state before heating, the echo signal is stored in the memory 25 as “pre-warming echo signal” and sent to the external computer device 6.

Next, the ultrasonic velocity change and fat information are calculated by the external computer device 6 (fat information calculation unit 12) (S105). That is, when an “echo signal after warming” and an “echo signal before warming” are sent from the control box 3, the ultrasonic velocity ratio (V ′ / V) is calculated based on the above-described equation (2). To do. Furthermore, based on this result, fat determination (determination of the presence or absence of fatty liver) is performed, or a fat ratio is calculated from comparison with reference data obtained in advance, and the ultrasonic velocity change ratio and fat information of the calculation result are used as numerical values or characters It is displayed on the screen of the external computer device 6.
By the measurement procedure described above, fat diagnosis based on changes in ultrasonic velocity can be performed.

  In the fat diagnosis system A, the external computer device 6 (general-purpose computer device) is used. However, the same hardware configuration of the CPU, memory, input device, and display device is incorporated in the control box 3 as (2 The external computer device 6 may be substituted by realizing the calculation processing function and the numerical value (character) display function of the calculation result by the control box 3. In that case, the fat information calculation unit 12 is configured by the control box 3.

(Embodiment 2 (reference example) )
FIG. 6 is an external view of a fat diagnostic system B using a fat diagnostic apparatus 10a according to another embodiment of the present invention, and FIG. 7 is a diagram showing components of the fat diagnostic apparatus 10a. The same components as those in FIGS. 1 and 2 are denoted by the same reference numerals, and a part of the description is omitted.
In this embodiment, a probe holder 15 to which any one of the main probe 2 and the sub probe 4 is attached is used instead of the probe holder 5 in FIGS. That is, the probe holder 15 is formed with a composite hole 15a formed so that the hole for inserting the sub probe 4 overlaps the central portion of the hole for inserting the main probe 2. One probe can be inserted alternately. The specific shape of the hole 15a is processed according to the outer shape of the main probe 2 and the sub probe 4 to be mounted. In the present embodiment, the rectangular holes and the circular holes are overlapped.
The control box 3a basically has the same function as the control box 3 described with reference to FIG. 2, but the probe holder 15 is not provided with the switching mirror 5a shown in FIG. The portion for performing the switching operation of the switching mirror 5a from the third controller 26 is omitted, but the rest is the same as the control box 3 of FIG.

8 is an external view of the probe holder 15 as viewed from the front. FIG. 8A shows a state in which the main probe 2 is inserted into the hole 15a, and FIG. 8B shows a state in which the sub probe 4 is inserted into the hole 15a. Show.
The hole 15a of the probe holder 15 has one of the axes of the ultrasonic waves irradiated from the main probe 2 in the axial direction of the ultrasonic waves irradiated from the sub probe 4 (the ultrasonic axis of the transducer at the center of the main probe 2). ) So that the irradiation position of the sub probe 4 can be grasped at the time of image diagnosis by the main probe 2.

  The vibrator 2a of the main probe 2 and the vibrator 4a of the sub probe 4 are both slightly protruded from the lower surface of the probe holder 15 so as to be in contact with the body surface while being inserted into the probe holder 15. When performing a fat diagnosis, the probe holder 15 is brought into contact with the body surface. However, in order to reduce the operation burden, the articulated arm 15b of FIG. 6 is used to fix and hold the probe holder 15 on the body surface of the measurement site. Used. Needless to say, measurement can be performed even if the probe holder 15 is held with one hand and the probe is exchanged or operated with the other hand without using the articulated arm 15b.

Next, the measurement procedure by the fat diagnostic system B (including the fat diagnostic device 10a) will be described. In this case as well, measurement is performed based on the flowchart of FIG.
First, a fat measurement position is searched and determined by image diagnosis by the ultrasonic diagnostic apparatus 1 (S101). That is, the main probe 2 is set in the probe holder 15 and the ultrasonic diagnostic apparatus 1 is operated to take a B-mode image by a pulse wave of about 3 MHz, and this is displayed on the screen to perform image diagnosis and is suitable for fat measurement. Search the measured position. At this time, the search may be performed so as to obtain a clear image with higher resolution by further increasing the frequency of the pulse wave as necessary.

  Next, heating control by the control box 3a (fat measurement control unit 11) is performed on the determined measurement position (S102). That is, the main probe 2 is removed from the probe holder 15 and the sub probe 4 is inserted. Then, the controller 26 sets the switch 23 on the high-frequency power source 21 side, turns on the high-frequency power source 21 and irradiates the heating ultrasonic wave via the sub probe 4. If the ultrasonic wave to be irradiated is 0.5 MHz to 3 MHz, the position of the liver can be efficiently heated, but the irradiation is preferably performed at about 0.7 MHz to 1 MHz. And heating is maintained until a heating area | region raises about 0.5 degreeC-2 degreeC, and is stabilized. For example, the heating time becomes stable after about 30 seconds.

  Next, the heating is stopped, and the echo signal is measured in the temperature rising state immediately after the heating is stopped (S103). That is, using the sub-probe 4 as it is, operating the controller 26 to switch the switch 23 to the pulsar / receiver circuit side 22 to transmit a pulse wave through the sub-probe 4 and to wait for and receive an echo signal. . The received echo signal is stored in the memory 25 as an “echo signal after heating” and is sent to the external computer device 6 (fat information calculation unit 12).

  Next, after the measurement of the “echo signal after warming” is completed, a predetermined time set in advance as the time required to return to normal temperature is further passed (for example, after about 10 to 20 seconds have passed). The echo signal when the temperature is lowered to the normal temperature before the temperature is measured (S104). That is, while the switch 23 is left as it is, a pulse wave is transmitted again through the sub probe 4 and an echo signal is awaited and received. Since the received echo signal has returned to the same signal as the normal temperature state before warming, it is stored in the memory 25 as “pre-warm echo signal” and sent to the external computer device 6.

Next, the ultrasonic velocity change and fat information are calculated by the external computer device 6 (fat information calculation unit 12) (S105). That is, when the “echo signal after warming” and the “echo signal before warming” are sent from the control box 3a, the ultrasonic velocity ratio (V ′ / V) is calculated based on the above-described equation (2). To do. Furthermore, based on this result, fat determination (determination of the presence or absence of fatty liver) is performed, or a fat ratio is calculated from comparison with reference data obtained in advance, and the ultrasonic velocity change ratio and fat information of the calculation result are used as numerical values or characters It is displayed on the screen of the external computer device 6.
By the measurement procedure described above, fat diagnosis based on changes in ultrasonic velocity can be performed.

(Embodiment 3)
FIG. 9 is an external view showing a fat diagnostic system C which is still another embodiment of the present invention. FIG. 10 is a block diagram showing a configuration of a portion corresponding to the fat diagnosis accessory device 30 in the fat diagnosis system C. The same components as those in FIGS. 1 and 2 are given the same reference numerals, and a part of the description is omitted.

The fat diagnostic system C includes an ultrasonic diagnostic apparatus 1, a main probe 2, a control box (dedicated board) 31, a secondary probe 4, a probe holder 5 having a switching mirror 5a for switching probes, and an external computer apparatus. 6 and a transmission line 32 for transmitting an echo signal between the ultrasonic diagnostic apparatus 1 and the control box 31. Among these, the control box 31, the sub probe 4, the probe holder 5, the external computer device 6, and the transmission line 32 constitute the fat diagnostic accessory device 30.
In this fat diagnostic accessory device 30, fat diagnosis is not performed using only the components retrofitted to the ultrasonic diagnostic device 1, but echoes measured using the existing ultrasonic diagnostic device 1 and the main probe 2. A fat diagnosis is performed using the signal. Therefore, since it is different from the “fat diagnostic device” of Embodiments 1 and 2 in which fat diagnosis can be performed only with the components that are retrofitted, it is referred to as “fat diagnostic accessory device”.

As the ultrasonic diagnostic apparatus 1 used in the present embodiment, an apparatus having an external output terminal that can extract a raw echo signal (RF signal) acquired via the main probe 2 to the outside is used. Some commercially available ultrasonic diagnostic equipment does not have such an external output terminal. In that case, the external output terminal can be connected by a simple operation such as installing an expansion card for adding an external output terminal. Add more.
The main probe 2 and the sub probe 4 in this embodiment are the same as those described in the first and second embodiments, but the sub probe 4 is used exclusively for heating, and the main probe 2 is used for diagnostic imaging. And used for transmission and reception of echo signals for fat diagnosis.

  The control box 31 receives a high-frequency power supply 21 that generates a heating ultrasonic wave, a receiver circuit 33 that receives an echo signal transmitted from an external output terminal of the ultrasonic diagnostic apparatus 1 via a transmission line 32, and receives the signal. An A / D converter 34 for converting the echo signal into a digital signal, a buffer memory 35 for adjusting the transmission speed for sending the echo signal to the external computer device 6, and further, driving the heating ultrasonic wave and switching the switching mirror 5a A controller 36 is provided for performing operation, receiving an echo signal by the receiver circuit 33, and controlling transmission of the echo signal by the buffer memory 35.

  Therefore, the control box 31 functions as a heating control unit 41 that performs control for heating the measurement site by transmitting an ultrasonic wave from the high-frequency power source 21 via the sub probe 4, and the ultrasonic diagnostic apparatus 1 uses the control box 31. It functions as an echo signal transmission control unit 42 that performs control to transmit a large number of echo signals that can be acquired to the external computer 6.

The external computer device 6 performs calculation according to the above-described equation (2) in a partial section corresponding to the echo signal from the liver among the echo signals before and after heating output from the control box 31 (echo signal transmission control unit 42). And an arithmetic process for calculating an ultrasonic velocity change (in this case, an ultrasonic velocity ratio) is performed.
That is, the waveform shift of the echo signal before and after heating is based on the echo signal received after heating and the echo signal received before heating, using the same principle and method as the conventional example described in FIG. A quantity (Δτ) is calculated, and a process of calculating a pulse interval (τ) between tissue boundaries in the measurement region is performed. And based on Formula (2), the process which calculates the ultrasonic velocity ratio (V '/ V) of each partial area is performed.
In this way, the external computer device 6 functions as a fat information calculation unit 43 that calculates fat information including changes in ultrasonic velocity based on the measurement results of echo signals before and after heating.

In the present embodiment, the data transmitted to the external computer device 6 (fat information calculation unit 43) is a large number of echo signal data acquired by the multi-channel main probe 2, so that image formation is possible. It is data. Therefore, an image display of an ultrasonic velocity change image and a fat distribution image can be performed using these echo signal data transmitted before and after heating.
Therefore, in the present embodiment, the value of the ultrasonic velocity ratio and the fat information (fat determination, fat ratio) can be expressed numerically on the display device, but by displaying the fat distribution image, the fat based on the fat distribution image is displayed. Diagnosis becomes possible.

Next, the measurement procedure by the fat diagnostic system C (including the fat diagnostic accessory device 31) will be described based on the flowchart of FIG.
First, a fat measurement position is searched and determined by image diagnosis by the ultrasonic diagnostic apparatus 1 (S201). That is, the switching mirror 5a is set so that the main probe 2 side is turned on, and the ultrasonic diagnostic apparatus 1 is operated to take a B-mode image by a pulse wave of about 3 MHz, and this is displayed on the screen to perform image diagnosis. Search for a measurement position suitable for fat measurement. At this time, the search may be performed so as to obtain a clear image with higher resolution by further increasing the frequency of the pulse wave as necessary.

  Next, heating control by the control box 31 (heating control unit 41) is performed on the determined measurement position (S202). That is, the controller 36 of the control box 31 is operated to switch the switching mirror 5 a so that the sub probe 4 side is turned on, the high frequency power supply 21 is turned on, and the heating ultrasonic wave is irradiated through the sub probe 4. If the ultrasonic wave to be irradiated is 0.5 MHz to 3 MHz, the position of the liver can be efficiently heated, but the irradiation is preferably performed at about 0.7 MHz to 1 MHz. And heating is maintained until a heating area | region raises about 0.5 degreeC-2 degreeC, and is stabilized. For example, the heating time becomes stable after about 30 seconds.

  Next, the heating is stopped, and the echo signal is measured in the temperature rising state immediately after the heating is stopped (S203). That is, the controller 36 is operated to switch the switching mirror 5a so that the main probe 2 side is turned on. Then, pulse waves are transmitted and received while scanning each transducer of the multi-channel main probe 2, and the number of echo signals necessary for image formation is acquired via the ultrasonic diagnostic apparatus 1. At the same time, the echo signal transmitted from the transmission line 32 is received by the receiver circuit 33 of the control box 31 (echo signal transmission control unit 42), A / D converted by the A / D converter 34, and external computer apparatus 6 (fat information calculation unit 43) as “echo signal after heating”. At this time, the data is transmitted while the transmission speed is adjusted by the buffer memory 35.

  Next, after the measurement of the “echo signal after warming” is completed, a predetermined time set in advance as the time required to return to normal temperature is further passed (for example, after about 10 to 20 seconds have passed). An echo signal is measured when the temperature is lowered to a normal temperature before the temperature (S204). That is, the switching mirror 5 a is left as it is, and pulse waves are transmitted and received again via the main probe 2, and the number of echo signals necessary for image formation is acquired via the ultrasonic diagnostic apparatus 1. At the same time, the echo signal transmitted from the transmission line 32 is received by the receiver circuit 33 of the control box 31 (echo signal transmission control unit 42), A / D converted by the A / D converter 34, and external computer apparatus 6 (fat information calculation unit 43) is transmitted as an “echo signal before heating”. Also at this time, transmission is performed while the transmission speed is adjusted by the buffer memory 35.

  Next, ultrasonic velocity change and fat information are calculated by the external computer device 6 (fat information calculation unit 43), and an ultrasonic velocity change image and a fat distribution image are formed (S205). That is, when the “post-warming echo signal” and the “pre-warming echo signal” are sent from the control box 31 (echo signal transmission control unit 42), the ultrasonic velocity ratio based on the above-described equation (2). (V ′ / V) is calculated. By performing this operation on all the echo signals required for image formation, an ultrasonic velocity change image is formed. Further, a fat distribution image is formed by extracting a negative region of the ultrasonic velocity change image. These images are displayed on the screen of the external computer device 6.

  It should be noted that fat determination (determination of the presence or absence of fatty liver) is performed in the same manner as in the first and second embodiments based on a part of the number of image-formable echo signals transmitted to the external computer device 6 or in advance. The fat ratio may be calculated from the comparison with the obtained reference data and displayed on the screen as a numerical value or a character together with the fat image display.

At that time, a separate signal line for direct communication is provided between the ultrasonic diagnostic apparatus 1 and the external computer apparatus 6 and an echo signal ("echo signal after warming" or "before warming" transmitted to the external computer apparatus 6 is provided. If the same echo signal as “echo signal”) is also accumulated on the ultrasonic diagnostic apparatus 1 side and a corresponding B-mode image is displayed on the ultrasonic diagnostic apparatus 1 side, the screen on the ultrasonic diagnostic apparatus 1 side is displayed. Since the region of interest (ROI) information set above can be transmitted to the external computer device 6 side, fat information in the corresponding region of interest on the external computer device 6 side can be calculated accordingly. become.
With the above measurement procedure, fat diagnosis can be performed using an ultrasonic velocity change image, a fat distribution image, or the like.

(Modified embodiment)
The present invention is not limited to the above embodiments, and various modifications can be made without departing from the spirit of the present invention.
For example, in each of the above embodiments, the post-heating echo signal is measured first, and the pre-heating echo signal is measured later, but the measurement can be performed even if the measurement order is reversed.

In each of the above embodiments, the cylindrical sub-probe 4 formed of a single-channel vibrator is used. However, a vibrator having a small number of channels (for example, 2 to 5 channels) may be used.
In that case, in Embodiments 1 and 2 in which fat diagnosis is performed via the sub-probe 4, individual measurement may be performed in parallel at measurement points of a small number of channels, and averaging processing may be performed.

  In the third embodiment, only one control box 31 is provided. However, the control box 31 may be divided into two control boxes for heating control and echo signal transmission control. In that case, the controller 36 is provided in each control box. In addition, since the fat diagnosis can be performed by the image in the third embodiment, it is useful not only for the measurement of the deep part of the living body but also for diagnosing the property (fibrous or lipidic) of the plaque near the body surface, for example, the carotid artery. Information can be obtained.

  INDUSTRIAL APPLICABILITY The present invention can be used as a fat diagnostic apparatus that attaches to an ultrasonic diagnostic apparatus and performs fat diagnosis, and a fat diagnostic accessory apparatus.

1 Ultrasonic diagnostic equipment 2 Main probe (multi-channel probe)
2a vibrator 3, 3a control box 4 sub probe (1 channel probe)
4a vibrator 5 probe holder 5a switching mirror 5b side wall 5c opening 5d opening (exit port)
5e Opening 5f Sheet 6 External computer device 10, 10a Fat diagnosis device 11 Fat measurement control unit 12 Fat information calculation unit 21 High frequency power supply (ultrasonic source)
22 Pulser / receiver circuit 23 Switch 24 A / D converter 25 Memory 26 Controller 31 Control box 32 Transmission line 33 Receive circuit 34 A / D converter 35 Buffer memory 36 Controller 41 Heating control unit 42 Echo signal transmission control unit 43 Fat Information calculator

Claims (6)

Acquired echo signals from the measurement site using a multi-channel main probe and attached to an ultrasound diagnostic device that performs image diagnosis using the ultrasound image formed by the echo signals. A fat diagnostic apparatus for performing a fat diagnosis by calculating an ultrasonic velocity change,
The fat diagnostic apparatus includes a sub-probe capable of ultrasonic irradiation for heating,
Heating control is performed by irradiating the measurement site with the ultrasonic wave generated by the heating ultrasonic source through the auxiliary probe, and a pulse signal is transmitted through the auxiliary probe before and after the heating. A fat measurement control unit that performs control to measure the echo signal of
A fat information calculation unit for calculating fat information including an ultrasonic velocity change from the echo signals before and after the heating;
A probe in which the main probe and the sub-probe are mounted at the same time , a common emission port for emitting the ultrasonic wave emitted from each probe to the measurement site is provided, and either one of the ultrasonic waves is selectively transmitted and received A holder ,
A common standoff filled with a fluid ultrasonic propagation medium is formed so as to be in contact with the transducer of each probe, and an ultrasonic wave emitted from one of the probes is emitted into the standoff. A fat diagnostic apparatus , characterized in that a switching mechanism for switching so as to lead to is attached .
The fat diagnostic apparatus according to claim 1, wherein the sub probe includes a one-channel transducer. The fat diagnostic apparatus according to claim 1, wherein the fat information calculation unit outputs an ultrasonic velocity change or fat information as a numerical value or character data. The fat diagnostic apparatus according to any one of claims 1 to 3, wherein the fat measurement control unit transmits ultrasonic waves for heating of 0.5 MHz to 3 MHz. The fat diagnostic apparatus is connected to an external computer device that has a display device and can perform calculation processing.
Fat diagnostic apparatus according to any one of the fat information calculation unit according to claim 1 to claim 4 provided in the external computer device. Acquired echo signals from the measurement site using a multi-channel main probe and attached to an ultrasound diagnostic device that performs image diagnosis using the ultrasound image formed by the echo signals. A fat diagnosis accessory device for performing a fat diagnosis by calculating an ultrasonic velocity change,
The accessory device for fat diagnosis includes a secondary probe capable of ultrasonic irradiation for heating,
A heating control unit that performs heating control by irradiating a measurement site with ultrasonic waves generated by an ultrasonic source for heating via the auxiliary probe;
An echo signal transmission control unit for performing control to acquire and transmit echo signals before and after heating measured using the main probe and the ultrasonic diagnostic apparatus from the ultrasonic diagnostic apparatus;
A fat information calculation unit for calculating fat information including ultrasonic velocity change from the transmitted echo signals before and after heating;
A probe in which the main probe and the sub-probe are mounted at the same time , a common emission port for emitting the ultrasonic wave emitted from each probe to the measurement site is provided, and either one of the ultrasonic waves is selectively transmitted and received A holder ,
A common standoff filled with a fluid ultrasonic propagation medium is formed so as to be in contact with the transducer of each probe, and an ultrasonic wave emitted from one of the probes is emitted into the standoff. An attachment device for fat diagnosis, characterized in that a switching mechanism for switching to lead to is attached.

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