Ultrasound diagnostic device, method of operating the ultrasound diagnostic device, and operating program for the ultrasound diagnostic device

Abstract

This invention provides an ultrasound diagnostic device, an operating method for the ultrasound diagnostic device, and an operating program for the ultrasound diagnostic device that can suppress a decrease in the accuracy of calculating the attenuation rate even when the measurement conditions are changed. [Solution] The selection unit selects a reference signal from among multiple reference signals in the reference signal DB that corresponds to the measurement target area. The calculation unit calculates the attenuation rate of the measurement signal based on the measurement signal obtained by measuring the patient and the selected reference signal.

Description

Technical Field

[0001] The technology of the present disclosure relates to an ultrasonic diagnostic apparatus, an operation method of an ultrasonic diagnostic apparatus, and an operation program of an ultrasonic diagnostic apparatus.

[0002] Quantitative evaluation techniques for hepatic fat using ultrasonic attenuation have attracted attention. In the quantitative evaluation techniques, the reference method is mainly adopted due to its high calculation accuracy of the attenuation rate. The reference method is a method of calculating the attenuation rate based on, for example, a reference signal obtained by measuring a phantom and a measurement signal obtained by actually measuring a subject (see Non-Patent Document 1).

Prior Art Documents

Non-Patent Documents

[0003]

Non-Patent Document 1

Summary of the Invention

Problems to be Solved by the Invention

[0004] In measurement, there are cases where changes in measurement conditions are required, such as changing the measurement target region to a region avoiding structures such as blood vessels and tissue boundaries. Further, in conventional quantitative evaluation techniques for hepatic fat, the liver is mainly observed with a body surface probe, and the focus position, frequency, etc. of the transmitted wave are generally fixed. However, recently, there has been a demand to observe the liver with an intracorporeal insertion probe, or to observe the pancreas instead of the liver. In such cases, if there is only one reference signal, it may not be suitable for the changed measurement conditions, and the calculation accuracy of the attenuation rate may decrease.

[0005] One embodiment of the technology of this disclosure provides an ultrasound diagnostic apparatus, a method for operating the ultrasound diagnostic apparatus, and an operating program for the ultrasound diagnostic apparatus that can suppress a decrease in the accuracy of calculating the attenuation rate even when the measurement conditions are changed. [Means for solving the problem]

[0006] The ultrasound diagnostic apparatus of this disclosure includes a processor, which selects a reference signal from among a plurality of reference signals according to the measurement conditions, and calculates the attenuation rate of the measurement signal based on the measurement signal obtained by measuring the subject and the selected reference signal.

[0007] The measurement conditions preferably consist of at least one of the following: the measurement area, the focus position of the transmitted wave, the gain applied to the echo signal, the frequency of the transmitted wave, the type of probe, and the organ being measured.

[0008] The measurement conditions preferably consist of at least one of the following: the measurement area, the focus position of the transmitted wave, the gain applied to the echo signal, and the frequency of the transmitted wave.

[0009] The processor preferably detects a measurement target area that satisfies the detection conditions and selects a reference signal corresponding to the detected measurement target area.

[0010] The detection conditions preferably include conditions relating to the distance to the organ being measured, and conditions relating to the intensity of the echo signal.

[0011] The probe type is preferably either a surface probe or an internally implantable probe.

[0012] The organ to be measured is preferably either the liver or the pancreas.

[0013] It is preferable that the calculation result information of the attenuation rate is displayed on the display unit.

[0014] The calculation results information is preferably presented as a color map that represents the attenuation rate level using different colors.

[0015] It is preferable that the reference signal used to calculate the attenuation rate is displayed on the display unit along with the calculation result information.

[0016] The reference signal is preferably one of the following: a measurement signal obtained using a phantom, a representative value of the measurement signals of multiple representative subjects, or a measurement signal obtained using a phantom corrected with the representative value of the measurement signals of multiple representative subjects.

[0017] The reference signal is preferably generated based on the transmit beam profile and gain profile.

[0018] The method for operating the ultrasound diagnostic apparatus of this disclosure includes selecting a reference signal from among a plurality of reference signals according to the measurement conditions, and calculating the attenuation rate of the measurement signal based on the measurement signal obtained by measuring the subject and the selected reference signal.

[0019] The operating program for the ultrasound diagnostic apparatus of this disclosure causes a computer to perform a process that includes selecting a reference signal from among a plurality of reference signals according to the measurement conditions, and calculating the attenuation rate of the measurement signal based on the measurement signal obtained by measuring the subject and the selected reference signal. [Effects of the Invention]

[0020] The technology disclosed herein provides an ultrasound diagnostic apparatus, an operating method for the ultrasound diagnostic apparatus, and an operating program for the ultrasound diagnostic apparatus that can suppress a decrease in the accuracy of calculating the attenuation rate even when the measurement conditions are changed. [Brief explanation of the drawing]

[0021] [Figure 1] This figure shows an ultrasound diagnosis using a surface-mounted probe. [Figure 2]This is a block diagram showing the electrical configuration of an ultrasonic diagnostic apparatus. [Figure 3] This is a block diagram showing the detailed configuration of a control unit. [Figure 4] This is a block diagram showing a processing unit of a CPU. [Figure 5] This is a diagram showing a reference signal DB. [Figure 6] This is a diagram showing a setting information table. [Figure 7] This is a diagram showing a state of changing to a measurement target region that avoids blood vessels. [Figure 8] This is a diagram showing an aspect of selecting a reference signal corresponding to a measurement target region. [Figure 9] This is a diagram showing an aspect of selecting setting information corresponding to a measurement target region. [Figure 10] This is a diagram showing the attenuation rate when using Equation (2). [Figure 11] This is a diagram showing a diagnostic screen. [Figure 12] This is a diagram showing the processing procedure of the ultrasonic diagnostic apparatus. [Figure 13] This is a diagram showing the second embodiment in which a measurement target region satisfying a detection condition is detected, and a reference signal corresponding to the detected measurement target region is selected. [Figure 14] This is a diagram showing an aspect of selecting a reference signal corresponding to a focus position. [Figure 15] This is a diagram showing an aspect of selecting a reference signal corresponding to a gain. [Figure 16] This is a diagram showing an aspect of selecting a reference signal corresponding to a frequency. [Figure 17] This is a diagram showing a state of ultrasonic diagnosis using an in-vivo insertion probe. [Figure 18] This is a specification table of the body surface probe and the in-vivo insertion probe. [Figure 19] This is a specification table of the body surface probe and the in-vivo insertion probe. [Figure 20] This is a diagram showing an aspect of selecting a reference signal corresponding to a probe. [Figure 21] This is a diagram showing an example in which the pancreas is set as the measurement target organ. [Figure 22] This figure shows how to select a reference signal according to the organ being measured. [Figure 23] This figure shows a method for displaying a color map of the attenuation rate. [Figure 24] This figure shows an example where a measurement signal obtained using a phantom is used as a reference signal. [Figure 25] This figure shows an example where the average value of measurement signals from multiple representative patients is used as the reference signal. [Figure 26] This figure shows an example where a measurement signal obtained using a phantom is corrected with the average value of measurement signals from multiple representative patients to create a reference signal. [Figure 27] This figure shows an example of generating a reference signal by adding the transmit beam profile and the gain profile. [Modes for carrying out the invention]

[0022] [First Embodiment] As an example, as shown in Figure 1, the ultrasound diagnostic device 10 comprises a main unit 11, a surface probe 12, a display 13, and an input device 14. The main unit 11 and the surface probe 12 are connected by a cable 15. The surface probe 12 is held by an operator OP, such as an ultrasound technician, and its tip is placed on the abdominal surface of a patient P who is lying supine on a bed 16. A transmitted wave TU is emitted from the tip of the surface probe 12. The transmitted wave TU reaches the liver Li. Patient P is an example of a "subject" related to the technology of this disclosure. The liver Li is an example of a "measurement target organ" related to the technology of this disclosure.

[0023] The display 13 displays an ultrasound image, in this case a B (Brightness) mode image 17, based on the reflected wave RU reflected within the patient P's body in response to the transmitted wave TU. The B mode image 17 shows, for example, subcutaneous tissue and the liver Li. The display 13 also displays various screens, such as a patient P registration screen and a screen for setting the focus position of the transmitted wave TU. These various screens have GUI (Graphical User Interface) operation functions. The device body 11 receives operation instructions from the input device 14 through these various screens. The input device 14 includes a keyboard, mouse, touch panel, and microphone for voice input. The display 13 is an example of a "display unit" related to the technology of this disclosure.

[0024] The main unit 11, the display 13, and the input device 14 are mounted on a cart 18. The cart 18 has wheels 19 and can be moved around within the medical facility.

[0025] As an example, as shown in Figure 2, the surface probe 12 incorporates a transducer array 25 at its tip. The transducer array 25 is composed of multiple (e.g., 64 to 192) aligned transducers 26. The transducer array 25 emits a transmission wave TU and receives a reflected wave RU. Transducer arrays 25 can be of various types, such as convex, linear, and sector. In the convex type, the transducers 26 are arranged in a curved shape, forming a fan-shaped transmission wave TU. In the linear type, the transducers 26 are arranged in a straight line, forming a rectangular transmission wave TU. In the sector type, the transducers 26 are densely arranged in a narrow opening, forming a fan-shaped transmission wave TU by electronic scanning. In this example, the convex type is preferred for observing the abdomen of patient P. In addition to the transducer array 25, the tip of the surface probe 12 also incorporates an acoustic lens, etc.

[0026] The main unit 11 of the device comprises a multiplexer 30, a transmitting unit 31, a receiving unit 32, an image generation unit 33, and a control unit 34. Transducers 26 are connected to the multiplexer 30. The transmitting unit 31 and the receiving unit 32 are also connected to the multiplexer 30. The multiplexer 30 is responsible for the transmission control of the transmitted wave TU and the reception control of the reflected wave RU. The transmission control of the transmitted wave TU is a control that generates the transmitted wave TU from the selected transducer 26 by sending a transmission pulse to the selected transducer 26 from among the multiple transducers 26. The reception control of the reflected wave RU is a control that distributes the electrical signal (hereinafter referred to as the echo signal) corresponding to the reflected wave RU received by each transducer 26 to the appropriate channel of the receiving unit 32.

[0027] The transmitting unit 31 includes a transmitting pulse generator 35, a transmitting delay circuit 36, and a pulser 37. The transmitting pulse generator 35 generates a transmitting pulse with a set frequency and pulse width and outputs it to the transmitting delay circuit 36. The transmitting delay circuit 36 ​​adjusts the focus position of the transmitting wave TU by controlling the timing of supplying the transmitting pulse to each transducer 26. Specifically, the transmitting delay circuit 36 ​​adjusts the focus position to a relatively shallow position by supplying the transmitting pulse to the central transducer 26 first and then to the end transducers 26 with a delay. On the other hand, the transmitting delay circuit 36 ​​adjusts the focus position to a relatively deep position by supplying the transmitting pulse to the end transducers 26 first and then to the central transducers 26 with a delay. The pulser 37 supplies the transmitting pulse to the transducers 26 through the multiplexer 30.

[0028] The receiving section 32 includes an analog front-end circuit 38 and a beamforming circuit 39. The analog front-end circuit 38 has a low-noise amplifier (hereinafter referred to as LNA (Low Noise Amplifier)) 40, a time-gain compensation amplifier (hereinafter referred to as TGC (Time Gain Compensation)) 41, an anti-aliasing filter (hereinafter referred to as AAF (Anti-Aliasing Filter)) 42, and an analog-to-digital converter (hereinafter referred to as ADC (Analog-to-Digital Converter)) 43. Although only one channel of the analog front-end circuit 38 is shown in Figure 2, there are actually multiple channels (for example, 16 to 256 channels).

[0029] The LNA40 amplifies the echo signal corresponding to the reflected wave RU from the transducer 26 to a set level. The LNA40 outputs the amplified echo signal to the TGC41 and the control unit 34. In the following, the echo signal output from the LNA40 to the control unit 34 will be referred to as the measurement signal 62 (see Figure 4).

[0030] TGC41 applies a gain to the echo signal according to its propagation distance to compensate for attenuation due to the propagation distance of the echo signal. In other words, TGC41 enhances the deep (distal) echo signal compared to the shallow (proximal) echo signal. This equalizes the brightness and contrast of ultrasound images such as the B-mode image 17. TGC41 outputs the analog time-gain corrected echo signal to AAF42. The gain applied to the echo signal in TGC41 is an example of the "gain applied to the echo signal" related to the technology of this disclosure.

[0031] AAF42 is a so-called low-pass filter that prevents aliasing noise by removing high-frequency components exceeding the Nyquist frequency from the echo signal. ADC43 converts the analog echo signal that has passed through AAF42 into a digital echo signal and outputs it to beamforming circuit 39. The beamforming circuit 39 corrects the time difference of each echo signal from the analog front-end circuit 38 and then adds them together. In this way, the beamforming circuit 39 obtains beamforming data necessary for generating an ultrasound image. The beamforming data includes amplitude information and phase information of each echo signal. The beamforming circuit 39 outputs the beamforming data to the image generation unit 33.

[0032] The image generation unit 33 applies digital time gain correction to the beamforming data according to the gain of the setting information 63. The image generation unit 33 generates an ultrasound image based on the beamforming data. In addition to the example B-mode image 17, the image generation unit 33 can also generate M (Motion) mode images, Doppler images, etc., as ultrasound images. The image generation unit 33 configures a diagnostic screen 75 (see Figure 11) including the generated ultrasound image and displays it on the display 13.

[0033] The control unit 34 comprehensively controls the operation of each part, including the multiplexer 30, the transmitter 31, the receiver 32, and the image generation unit 33. Specifically, the control unit 34 connects each transducer 26 to the transmitter 31 and the receiver 32 via the multiplexer 30. The control unit 34 sets the focus position and frequency to the transmitter 31 and adjusts the timing and waveform of the transmission pulse. The control unit 34 sets the gain to the TGC 41 of the receiver 32 and sets beamforming conditions such as delay time to the beamforming circuit 39. The control unit 34 also causes the image generation unit 33 to generate an ultrasonic image according to the selected display mode.

[0034] The control unit 34 receives various operation instructions from the operator OP via the input device 14. These operation instructions include instructions to transmit the transmission wave TU, instructions to switch the display mode of the ultrasound image, and instructions to start and end the liver Li attenuation rate calculation process, which will be described later. Other operation instructions include instructions to start and end the liver Li attenuation rate calculation process, and instructions to change the measurement target area 70 (see Figure 4) for the liver Li attenuation rate. The control unit 34 performs control according to these operation instructions. The surface probe 12 may also be provided with switches for transmitting the transmission wave TU and / or for starting and ending the liver Li attenuation rate calculation process.

[0035] As an example, as shown in Figure 3, the control unit 34 includes storage 50, a CPU (Central Processing Unit) 51, and memory 52. ​​These storage 50, CPU 51, and memory 52 are interconnected via a bus line 53. The control unit 34 is an example of a "computer" according to the technology of this disclosure.

[0036] Storage 50 is, for example, a hard disk drive. Storage 50 stores various programs and various data associated with those programs. A solid-state drive may be used instead of a hard disk drive.

[0037] Memory 52 is a work memory for the CPU 51 to execute processing. The CPU 51 loads the program stored in storage 50 into memory 52 and executes processing according to the program. In this way, the CPU 51 comprehensively controls each part of the main body 11 of the device. CPU 51 is an example of a "processor" related to the technology of this disclosure. Note that memory 52 may be built into the CPU 51.

[0038] As an example, as shown in Figure 4, the storage 50 stores an operating program 55. The operating program 55 is a program that causes the CPU 51 to perform attenuation rate calculation processing, etc. In other words, the operating program 55 is an example of an "operating program for an ultrasonic diagnostic device" related to the technology of this disclosure. The storage 50 also stores a reference signal database (hereinafter referred to as DB (Data Base)) 56 and a setting information table 57.

[0039] As an example, as shown in Figure 5, the reference signal DB56 has a reference signal 60 registered for each measurement target area. The measurement target area is expressed as a distance in the depth direction from the body surface, for example, 1cm-5cm, 2cm-6cm, 3cm-7cm, etc. The measurement target area can be changed as appropriate by the operator OP (see Figure 7). The measurement target area is an example of the "measurement conditions" related to the technology of this disclosure.

[0040] The reference signal 60 shows a sharp increase in amplitude near the focus position, just before the measurement target area indicated by the dashed line 61, and then begins to decrease. Within the measurement target area, the amplitude gradually decreases. Furthermore, the rate of decrease in amplitude of the reference signal 60 decreases as the measurement target area becomes deeper.

[0041] As an example, as shown in Figure 6, the setting information table 57 registers the focus position of the transmitted wave TU, the gain applied to the echo signal, and the frequency of the transmitted wave TU for each measurement target area. The focus position and frequency register the values ​​that are actually set in the transmitting unit 31. The gain registers the values ​​that are actually set in the receiving unit 32 for each depth of gain.

[0042] The focus position is set to a shallow position within the measurement area, for example. Specifically, the focus position is 1 cm if the measurement area is 1 cm-5 cm, 2 cm if it is 2 cm-6 cm, and 3 cm if it is 3 cm-7 cm. In other words, as the measurement area gets deeper, the focus position is also set to a deeper position. However, by appropriately controlling the transmission delay of the transmitted wave, it is also possible to set a focus position with a certain depth range, such as 0.5 cm-1.5 cm for a measurement area of ​​1 cm-5 cm, 1.5 cm-2.5 cm for 2 cm-6 cm, and 2.5 cm-3.5 cm for 3 cm-7 cm.

[0043] The gain is set higher in deeper areas than in shallow areas, regardless of the measurement area. Furthermore, the gain is set lower in the shallowest areas (1cm-3cm) closest to the body surface as the measurement area becomes shallower. The reason for setting a lower value in the shallowest areas is to prevent saturation of the echo signal at the shallowest depths.

[0044] The frequency is set lower the deeper the measurement area is. Specifically, the frequency is 7MHz for a measurement area of ​​1cm-5cm, 6MHz for 2cm-6cm, and 5MHz for 3cm-7cm.

[0045] Thus, the focus position, gain, and frequency are set to values ​​corresponding to the measurement area. These focus position, gain, and frequency are also examples of "measurement conditions" related to the technology of this disclosure. In the following, the set of focus position, gain, and frequency will be collectively referred to as setting information 63.

[0046] When an operator OP issues a command to start the attenuation rate calculation process via the input device 14, the operation program 55 is started. Once the operation program 55 is started, as shown in Figure 4, the CPU 51 works in cooperation with the memory 52 and other components to function as a signal acquisition unit 65, an instruction reception unit 66, a selection unit 67, a setting unit 68, and a calculation unit 69. These signal acquisition unit 65, instruction reception unit 66, selection unit 67, setting unit 68, and calculation unit 69, particularly the selection unit 67 and calculation unit 69, execute the attenuation rate calculation process. In addition to these individual processing units, the CPU 51 also functions as various other processing units.

[0047] The signal acquisition unit 65 acquires the measurement signal 62 from the LNA 40. The signal acquisition unit 65 outputs the measurement signal 62 to the calculation unit 69. Although not shown in the diagram, the signal acquisition unit 65 also outputs the measurement signal 62 to the image generation unit 33.

[0048] The instruction receiving unit 66 receives various operation instructions input by the operator OP through the input device 14. In particular, the instruction receiving unit 66 receives an instruction 70 to change the measurement target area of ​​the attenuation rate. The instruction receiving unit 66 outputs the change instruction 70 to the selection unit 67 and the setting unit 68.

[0049] The selection unit 67 reads out a reference signal 60 from among the multiple reference signals 60 registered in the reference signal DB 56 that corresponds to the measurement target area. The selection unit 67 outputs the read-out reference signal 60 to the calculation unit 69. Although not shown in the diagram, the selection unit 67 also outputs the read-out reference signal 60 to the image generation unit 33.

[0050] The setting unit 68 reads out the setting information 63 corresponding to the measurement target area of ​​the change instruction 70 from among the multiple setting information 63 registered in the setting information table 57. The setting unit 68 outputs the focus position and frequency from the read setting information 63 to the transmitting unit 31, and the gain to the receiving unit 32.

[0051] In the initial default settings when the attenuation rate calculation process is instructed to begin, the selection unit 67 reads a reference signal 60 corresponding to the 3cm-7cm measurement target area from the reference signal DB 56. Similarly, in the default settings, the setting unit 68 reads setting information 63 corresponding to the 3cm-7cm measurement target area from the setting information table 57.

[0052] As an example, as shown in Figure 7, if blood vessels such as the portal vein, hepatic vein, or hepatic artery, which may hinder the accurate calculation of the attenuation rate, are present in the current measurement area, the operator OP will issue an instruction 70 to change the measurement area to one that avoids the blood vessels. Figure 7 shows an example in which the measurement area is changed from 3cm-7cm to 1cm-5cm in order to avoid hepatic vein HV.

[0053] In such cases, as shown in Figure 8 as an example, the selection unit 67 reads a reference signal 60 corresponding to the measurement target area of ​​the change instruction 70, in this case the 1cm-5cm measurement target area, from the reference signal DB 56 and outputs it to the calculation unit 69. In other words, the selection unit 67 selects a reference signal 60 corresponding to the 1cm-5cm measurement target area instead of a reference signal 60 corresponding to the 3cm-7cm measurement target area.

[0054] As an example, as shown in Figure 9, the setting unit 68 reads setting information 63 corresponding to the measurement target area of ​​the change instruction 70, in this case the 1cm-5cm measurement target area, from the setting information table 57 and outputs it to the transmitting unit 31 and the receiving unit 32. In other words, the setting unit 68 sets the setting information 63 corresponding to the 1cm-5cm measurement target area in place of the setting information 63 corresponding to the 3cm-7cm measurement target area in the transmitting unit 31 and the receiving unit 32. In this way, the setting information 63 corresponding to the measurement target area of ​​the change instruction 70 is set, and as a result, not only the measurement target area, but also the focus position of the transmitting wave TU, the gain applied to the echo signal, and the reference signal 60 corresponding to the frequency of the transmitting wave TU are selected.

[0055] It should be noted that the blood vessels mentioned as an example are not the only things that can hinder the calculation of the attenuation rate. For example, various artifacts such as multiple reflections (reverb artifact), echoes from the secondary pole (sidelobe artifact), or refraction (refraction artifact) can also hinder the accurate calculation of the attenuation rate.

[0056] In Figure 4, the calculation unit 69 calculates the attenuation rate of the measurement signal 62 based on the measurement signal 62 from the signal acquisition unit 65 and the reference signal 60 from the selection unit 67. The calculation unit 69 outputs the attenuation rate calculation result 71 to the image generation unit 33. The calculation result 71 is an example of "calculation result information" related to the technology of this disclosure.

[0057] The unit of attenuation rate is dB / cm / MHz. If the attenuation rate is 0.6 dB / cm / MHz or less, it is diagnosed as normal (no fat deposition), and if it is 0.7 dB / cm / MHz or higher, it is diagnosed as a high possibility of fatty liver. In particular, if the attenuation rate is 1.0 dB / cm / MHz or higher, it is diagnosed as severe fatty liver, and the risk of liver dysfunction such as cirrhosis should also be considered.

[0058] When the attenuation rate of the reference signal 60 is αref, the depth of the shallow part is d1, the depth of the deep part is d2, the amplitude of the measurement signal 62 is Pf(d), the amplitude of the reference signal 60 is Pref(d), and the frequency is f, the calculation unit 69 calculates the attenuation rate α from the following formula (1).

number

number

[0059] As an example, as shown in Figure 10, when equation (2) is used, the attenuation rate α is the slope of the straight line L connecting the difference in amplitude between the measured signal 62 and the reference signal 60 at depth d1, Pf(d1)-Pref(d1), and the difference in amplitude between the measured signal 62 and the reference signal 60 at depth d2, Pf(d2)-Pref(d2). In other words, equation (2) is an equation that linearly approximates the attenuation rate using the difference in amplitude between the measured signal 62 and the reference signal 60 at depths d1 and d2. Note that in Figure 10, d1 = 3 cm and d2 = 7 cm.

[0060] As an example, as shown in Figure 11, the diagnostic screen 75 displays basic measurement information 76, including the measurement date and time, patient information, measurement target area, focus position, and frequency. The diagnostic screen 75 also displays a B-mode image 17 and the calculated attenuation rate 71. The B-mode image 17 displays a dashed line 61 indicating the measurement target area and numerical values ​​indicating the shallow and deep parts of the measurement target area superimposed on it. Furthermore, the diagnostic screen 75 displays a graph 77 showing the amplitude of the measurement signal 62 and reference signal 60 used to calculate the attenuation rate against depth. The operator OP diagnoses whether or not there are signs of fatty liver in the liver Li of patient P while viewing this diagnostic screen 75.

[0061] Next, the operation of the above configuration will be explained. First, the patient P is guided by the operator OP to lie supine on the bed 16. The operator OP turns on the power of the ultrasound diagnostic device 10, displays the patient P registration screen on the display 13, and inputs the patient information through the input device 14.

[0062] The operator OP grasps the surface probe 12 and places it against the abdominal surface of the patient P, and inputs a signal to transmit the transmitter wave TU through the input device 14. This drives the transmitter 31 and the multiplexer 30 under the control of the control unit 34, and the transmitter wave TU is emitted from the transducer array 25.

[0063] The transmitted wave TU propagates through the patient P's body, and a portion is reflected due to differences in acoustic impedance between tissues. The resulting reflected wave RU is received by the transducer array 25 and converted into an echo signal. Under the control of the control unit 34, the echo signal is digitized via the multiplexer 30 and analog front-end circuit 38 and input to the beamforming circuit 39. In the beamforming circuit 39, delay correction and summation processing are applied to the echo signal to generate beamforming data. The beamforming data is output from the beamforming circuit 39 to the image generation unit 33.

[0064] In the image generation unit 33, an ultrasound image, such as a B-mode image 17, is generated based on the beamforming data. Then, a diagnostic screen 75 including the B-mode image 17 is configured and displayed on the display 13.

[0065] The operator OP adjusts the position of the body surface probe 12 to a position suitable for observing liver Li while viewing the B-mode image 17 on the diagnostic screen 75. Then, the operator OP inputs a command to start the liver Li attenuation rate calculation process through the input device 14. This starts the operating program 55, and the CPU 51 of the control unit 34 functions as a signal acquisition unit 65, an instruction reception unit 66, a selection unit 67, a setting unit 68, and a calculation unit 69, as shown in Figure 4.

[0066] In the default settings, the selection unit 67 reads a reference signal 60 corresponding to the 3cm-7cm measurement target area from the reference signal DB 56 and outputs it to the calculation unit 69 and the image generation unit 33. Similarly, the setting unit 68 reads setting information 63 corresponding to the 3cm-7cm measurement target area from the setting information table 57 and outputs it to the transmission unit 31 and the reception unit 32.

[0067] The signal acquisition unit 65 receives the measurement signal 62 from the LNA 40. The measurement signal 62 is output from the signal acquisition unit 65 to the calculation unit 69 and the image generation unit 33.

[0068] In the calculation unit 69, the attenuation rate is calculated based on the measurement signal 62 and the reference signal 60. The calculation result 71 of the attenuation rate is output from the calculation unit 69 to the image generation unit 33.

[0069] As shown in Figure 11, the image generation unit 33 displays the calculation result 71 and a graph 77 of the measurement signal 62 and reference signal 60 used to calculate the attenuation rate on the diagnostic screen 75.

[0070] As shown in Figure 7, if hepatic vein HV or other factors that could hinder the accurate calculation of the attenuation rate are present in the current measurement target area, the operator OP inputs a change instruction 70 through the input device 14.

[0071] As an example, as shown in Figure 12, the change instruction 70 is received by the instruction receiving unit 66 (step ST100). The change instruction 70 is output from the instruction receiving unit 66 to the selection unit 67 and the setting unit 68.

[0072] As shown in Figure 8, the selection unit 67 reads a reference signal 60 corresponding to the measurement target area of ​​the change instruction 70 from the reference signal DB 56. The read reference signal 60 is output from the selection unit 67 to the calculation unit 69. In this way, a reference signal 60 corresponding to the measurement target area of ​​the change instruction 70 is selected (step ST110).

[0073] Furthermore, as shown in Figure 9, the setting unit 68 reads setting information 63 corresponding to the measurement target area of ​​the change instruction 70 from the setting information table 57. The read setting information 63 is output from the setting unit 68 to the transmission unit 31 and the reception unit 32. In this way, the setting information 63 corresponding to the measurement target area of ​​the change instruction 70 is set in the transmission unit 31 and the reception unit 32.

[0074] A transmit wave TU corresponding to the focus position and frequency of the setting information 63 is emitted from the transducer array 25, and the resulting reflected wave RU is received by the transducer array 25 (step ST130). The echo signal corresponding to the reflected wave RU is amplified to the set level by the LNA 40 and then output as a measurement signal 62 from the LNA 40 to the control unit 34. The gain of the setting information 63 is applied to the echo signal by the TGC 41 and digitized by the ADC 43. The digitized echo signal is converted into beamforming data by the beamforming circuit 39. The beamforming data is subjected to digital time gain correction according to the gain of the setting information 63 in the image generation unit 33. Then, the image generation unit 33 generates a B-mode image 17 based on the beamforming data and displays it on the diagnostic screen 75.

[0075] The signal acquisition unit 65 acquires the measurement signal 62 (step ST140). The measurement signal 62 is output to the calculation unit 69, where the attenuation rate is calculated based on the measurement signal 62 and the reference signal 60 (step ST150). The calculation result of the attenuation rate 71 is output to the image generation unit 33 and displayed on the diagnostic screen 75 as shown in Figure 11 (ST160).

[0076] As explained above, the CPU 51 of the control unit 34 functions as a selection unit 67 and a calculation unit 69. The selection unit 67 selects a reference signal 60 from among multiple reference signals 60 of the reference signal DB 56 that corresponds to the measurement target area. The calculation unit 69 calculates the attenuation rate of the measurement signal 62 based on the measurement signal 62 obtained by measuring patient P and the selected reference signal 60. The reference signal 60 selected by the selection unit 67 is a reference signal 60 suitable for calculating the attenuation rate of the measurement signal 62 in the measurement target area. Therefore, even if the measurement target area is changed, it is possible to suppress a decrease in the accuracy of the attenuation rate calculation.

[0077] In this first embodiment, the measurement condition is the measurement target area. Furthermore, as shown in Figure 9, the measurement condition also includes the focus position of the transmitting wave TU, the gain applied to the echo signal, and the frequency of the transmitting wave TU. Therefore, even if the measurement target area, the focus position of the transmitting wave TU, the gain applied to the echo signal, and the frequency of the transmitting wave TU are changed, it is possible to suppress a decrease in the accuracy of the attenuation rate calculation.

[0078] As shown in Figure 11, the calculated attenuation rate 71 is displayed on the display 13. Therefore, the operator OP can check the calculated attenuation rate 71 in real time. The operator OP can quickly diagnose whether or not there are signs of fatty liver in the liver Li of patient P. In addition, since the decrease in the accuracy of the attenuation rate calculation is suppressed, a highly accurate diagnosis can be made.

[0079] As shown in Figure 11, the reference signal 60 used to calculate the attenuation rate is displayed on the display 13 along with the calculation result 71. Therefore, the operator OP can confirm which reference signal 60 was actually used to calculate the attenuation rate and verify the validity of the diagnosis.

[0080] [Second Embodiment] In the first embodiment described above, an example was given in which the operator OP inputs an instruction 70 to change the measurement target area, but the embodiment is not limited to this.

[0081] As an example, as shown in Figure 13, the CPU 51 of this second embodiment functions as a detection unit 80 in addition to the processing units 65 to 69 of the first embodiment (except for the selection unit 67 and the calculation unit 69, which are not shown in Figure 13). The detection unit 80 receives a B-mode image 17 from the image generation unit 33. The detection unit 80 also receives detection conditions 81, which are stored in the storage unit 50.

[0082] Detection conditions 81 are conditions for detecting the measurement target area, which is considered not to hinder the calculation of the attenuation rate. Detection conditions 81 broadly include conditions related to the distance to the measurement target organ, in this case the liver Li, and conditions related to the intensity of the echo signal. The first condition related to the distance to the measurement target organ is that it is at least 1 cm away from the boundary between subcutaneous fat and liver Li. The second condition related to the distance to the measurement target organ is that it is at least twice the distance between the surface probe 12 and the boundary of liver Li. These conditions are based on the fact that the measurement signal 62 is greatly disturbed near the boundary between subcutaneous fat and liver Li, making it difficult to accurately calculate the attenuation rate.

[0083] The conditions regarding the intensity of the echo signal are that either of the above conditions regarding the distance of the first or second target organ is met, and the change in brightness corresponding to the intensity of the echo signal in the B-mode image 17 is within the threshold range. The threshold range is defined as a range in which blood vessels and various artifacts are absent, and the liver Li parenchyma is considered to be uniformly present.

[0084] The detection unit 80 analyzes the B-mode image 17 and detects a measurement target area that satisfies the detection conditions 81. The detection unit 80 outputs the detection result 82 of the measurement target area to the selection unit 67. The selection unit 67 reads a reference signal 60 corresponding to the detection result 82 from the reference signal DB 56 and outputs the read reference signal 60 to the calculation unit 69.

[0085] Thus, in the second embodiment, the detection unit 80 detects a measurement target area that satisfies the detection condition 81, and the selection unit 67 selects a reference signal 60 according to the detection result 82. This eliminates the need for the operator OP to input a change instruction 70 for the measurement target area. Furthermore, it is possible to always obtain a measurement signal 62 for a measurement target area that is considered to have no problems in calculating the attenuation rate. Alternatively, the B-mode image 17 may be input to a trained model, and the trained model may output a measurement target area that is considered to have no problems in calculating the attenuation rate.

[0086] The detection conditions 81 include conditions relating to the distance to the organ being measured and conditions relating to the intensity of the echo signal. Therefore, the measurement target area, which is considered not to hinder the calculation of the attenuation rate, can be detected easily and with high accuracy.

[0087] [Third Embodiment] As an example, as shown in Figure 14, the measurement condition may be limited to the focus position of the transmitting wave TU. In this case, the operator OP inputs a focus position change instruction 85 through the input device 14. Figure 14 shows an example of changing the focus position from 3 cm to 1 cm.

[0088] The reference signal DB56 stores multiple reference signals 60 corresponding to each focus position. The selection unit 67 reads the reference signal 60 corresponding to the focus position of the change instruction 85, in this case a 1cm focus position, from the reference signal DB56 and outputs it to the calculation unit 69. Although not shown in the diagram, the setting unit 68 also outputs the focus position of the change instruction 85 to the transmission unit 31.

[0089] Similarly, as shown in Figure 15 as an example, the measurement condition may be limited to the gain applied to the echo signal. In this case, the operator OP inputs a gain change instruction 87 through the input device 14. Figure 15 shows an example of changing the gain from a focus position of 3 cm to 1 cm.

[0090] The reference signal DB56 has multiple reference signals 60 registered for each gain. The selection unit 67 reads the reference signal 60 corresponding to the gain of the change instruction 87, in this case the gain for a focus position of 1 cm, from the reference signal DB56 and outputs it to the calculation unit 69. Although not shown in the diagram, the setting unit 68 also outputs the gain of the change instruction 87 to the receiving unit 32.

[0091] Alternatively, as shown in Figure 16 as an example, the measurement condition may be only the frequency of the transmitted wave TU. In this case, the operator OP inputs a frequency change instruction 89 through the input device 14. Figure 16 shows an example of changing the frequency from 6 MHz to 5 MHz.

[0092] The reference signal DB56 stores multiple reference signals 60 corresponding to various frequencies. The selection unit 67 reads the reference signal 60 corresponding to the frequency of the change instruction 89, in this case 5MHz, from the reference signal DB56 and outputs it to the calculation unit 69. Although not shown in the diagram, the setting unit 68 outputs the frequency of the change instruction 89 to the transmission unit 31. Note that the reference signal 60 at frequency 5MHz has a smaller amplitude reduction rate as it goes deeper compared to the reference signal 60 at frequency 6MHz. Thus, the measurement conditions are not limited to all of the following: the focus position of the transmitting wave TU, the gain applied to the echo signal, and the frequency of the transmitting wave TU; at least one of these is sufficient. Note that factors that may change any one of the following—the focus position of the transmitting wave TU, the gain applied to the echo signal, and the frequency of the transmitting wave TU—can be the patient P's body type, such as obesity or muscular build.

[0093] [Fourth Embodiment] As an example, as shown in Figure 17, the main unit 90 of the ultrasound diagnostic apparatus of this fourth embodiment can be connected to an internal insertion probe 91 in addition to the surface probe 12. The internal insertion probe 91 is a so-called ultrasound endoscope, and has an imaging unit (not shown) and a transducer array 93 arranged at the tip of a long, slender insertion unit 92. The insertion unit 92 is bendable, and the direction of the tip can be changed. The transducer array 93 is composed of multiple transducers (not shown). The transducer array 93 can be, for example, a convex type or a radial type. In the convex type, the transducers are arranged in a curved shape, forming a fan-shaped transmitted wave TU. In the radial type, the transducers are arranged circumferentially, forming a transmitted wave TU in all 360 degrees. The convex type is suitable for observing liver Li. In addition to the imaging unit and transducer array 93, an acoustic lens and the like are built into the tip of the internal insertion probe 91.

[0094] If the operator OP determines that it is difficult to measure the attenuation rate with the surface probe 12, for example, if patient P is obese, the operator OP uses the internal implantable probe 91. The operator OP inserts the internal implantable probe 91 through the mouth of patient P. The probe then travels through the esophagus E and then the stomach St to bring the tip of the internal implantable probe 91, where the transducer array 93 is located, to the observation position of the liver Li. The operator OP inputs a transmission instruction for the transmitted wave TU through the input device, and the transducer array 93 transmits the transmitted wave TU towards the liver Li. The display shows a B-mode image 94 based on the reflected wave RU reflected in response to the transmitted wave TU. As shown by the dashed line 61 in the B-mode image 94 and, as an example, in the specifications table 100 in Figure 18, the default measurement area for the internal implantable probe 91 is, for example, 1 cm to 2.5 cm. The range of the measurement area is, for example, between 1 cm to 2.5 cm and 3.5 cm to 5 cm. The frequency of the transmitted wave TU is, for example, 4 MHz to 9 MHz. Furthermore, the elevation focus is, for example, 2.5 cm, and the display depth is, for example, 5 cm. For comparison, the values ​​for the surface probe 12 are also included in Specifications Table 100.

[0095] As an example, as shown in the specifications table 105 in Figure 19, the typical values ​​for the focus position of the transmitted wave TU of the implantable probe 91, the gain applied to the echo signal, the frequency of the transmitted wave TU, and the display depth are roughly the same regardless of the type of transducer array 93. Typical values ​​are, for example, the maximum or median values. Similar to specifications table 100, specifications table 105 also includes the values ​​for the surface probe 12 for comparison.

[0096] As an example, as shown in Figure 20, the reference signal DB56 includes a reference signal 60 corresponding to the body surface probe 12, as well as a reference signal 60 corresponding to the internally implanted probe 91. By default, the reference signal 60 corresponding to the internally implanted probe 91 has a measurement target area of ​​1 cm to 2.5 cm. Furthermore, the amplitude of the reference signal 60 corresponding to the internally implanted probe 91 gradually decreases within the measurement target area of ​​1 cm to 2.5 cm. Although only one reference signal 60 corresponding to the internally implanted probe 91 is shown here, in reality, multiple reference signals 60 are prepared according to the measurement target area range in the specifications table 100 shown in Figure 18, and the focus position of the transmitted wave TU, the gain applied to the echo signal, and the frequency of the transmitted wave TU as shown in the specifications table 105 shown in Figure 19.

[0097] When the body surface probe 12 is replaced with an internally implanted probe 91 connected to the main body 90 of the device, the selection unit 67 reads a reference signal 60 corresponding to the internally implanted probe 91 from the reference signal DB 56 and outputs it to the calculation unit 69. Although not shown in the figure, the setting unit 68 also outputs setting information 63 corresponding to the internally implanted probe 91 to the transmission unit 31 and the reception unit 32. Thus, the measurement conditions may also depend on the type of probe. Even if the type of probe is changed, it is possible to suppress a decrease in the accuracy of calculating the attenuation rate of the measurement signal 62. Furthermore, by using the body surface probe 12 and the internally implanted probe 91 as the types of probes, all conceivable types can be covered.

[0098] Furthermore, a reference signal 60 may be selected according to the model name and / or part number of the implantable probe 91. A reference signal 60 may also be selected according to the type of transducer array 93, such as convex or radial. A reference signal 60 may also be selected according to the organ (e.g., liver or pancreas) observed with the implantable probe 91. In these cases, the model name and / or part number of the implantable probe 91, the type of transducer array 93, or the organ observed with the implantable probe 91 is input to the operator OP via the input device 14. Alternatively, the model name and / or part number of the implantable probe 91, the type of transducer array 93, or the organ observed with the implantable probe 91 may be obtained by reading from an RFID (Radio Frequency Identification) tag attached to the connector of the implantable probe 91 connected to the main unit 90. In addition, the organ being observed may be estimated from the ultrasound image, and a reference signal 60 may be selected according to the estimation result.

[0099] [Fifth Embodiment] In the embodiments described above, the liver (Li) was used as an example of the organ to be measured for the attenuation rate, but it is not limited to this. As an example, as shown in Figure 21, the pancreas (Pan) may also be used as the organ to be measured for the attenuation rate. In the case of the pancreas (Pan), the default measurement area is 3 cm-5 cm, as shown in the figure. 3 cm-5 cm corresponds to the typical depth of the pancreas (Pan) from the body surface. Although Figure 21 illustrates the case of a surface probe 12, the attenuation rate of the pancreas (Pan) may also be measured using an internally inserted probe 91.

[0100] As an example, as shown in Figure 22, the reference signal DB56 includes a reference signal 60 corresponding to liver Li, as well as a reference signal 60 corresponding to pancreas Pan. By default, the reference signal 60 corresponding to pancreas Pan has a measurement range of 3 cm to 5 cm, as mentioned above. The amplitude of the reference signal 60 corresponding to pancreas Pan gradually decreases within the measurement range of 3 cm to 5 cm. Although only one reference signal 60 corresponding to pancreas Pan is shown here, in reality, multiple reference signals 60 are available depending on the range of the measurement range, the focus position of the transmitting wave TU, the gain applied to the echo signal, and the frequency of the transmitting wave TU.

[0101] The operator OP inputs a change instruction 110 for the target organ to be measured via the input device 14. When a change instruction 110 is input to change the target organ from liver (Li) to pancreas (Pan), the selection unit 67 reads a reference signal 60 corresponding to pancreas (Pan) from the reference signal DB 56 and outputs it to the calculation unit 69. Although not shown in the figure, the setting unit 68 also outputs setting information 63 corresponding to pancreas (Pan) to the transmission unit 31 and the reception unit 32. In this way, the measurement conditions may also be the target organ to be measured. Even if the target organ to be measured is changed, it is possible to suppress a decrease in the accuracy of calculating the attenuation rate of the measurement signal 62. Furthermore, by setting the target organs to liver (Li) and pancreas (Pan), all conceivable target organs can be covered.

[0102] Note that while Figure 11 shows an example where the calculation result 71 itself is displayed as the attenuation rate calculation result information, this is not the only option. As an example, as shown in Figure 23, a color map 115 representing the attenuation rate level with color may be displayed as the attenuation rate calculation result information. The color map 115 is generated by calculating the attenuation rate for each subdivided region obtained by further subdividing the corresponding area, and then filling each subdivided region with a color corresponding to the calculated attenuation rate level.

[0103] The image generation unit 33 superimposes a color map 115 onto the B-mode image 17. The image generation unit 33 also displays a color bar 116 next to the B-mode image 17, indicating the attenuation rate level represented by the colors in the color map 115. This allows the operator OP to visually grasp the attenuation rate level. This facilitates the operator OP's judgment on whether the calculated attenuation rate result 71 is appropriate. The calculated result 71 itself may also be displayed along with the color map 115. Furthermore, while Figure 23 shows an example of the B-mode image 17 of the body surface probe 12, the color map 115 may also be superimposed onto the B-mode image 94 of the internally implanted probe 91 shown in Figure 17.

[0104] As an example, as shown in Figure 24, the reference signal 60 is a measurement signal 62 obtained by irradiating a phantom PH, which mimics the human body, with a transmitted wave TU at a focus position and frequency corresponding to the measurement target area. Alternatively, as an example, as shown in Figure 25, the reference signal 60 may be the average value of the measurement signals 62 of multiple representative patients P. Furthermore, as an example, as shown in Figure 26, the reference signal 60 may be a measurement signal 62 obtained using the phantom PH, corrected with the average value of the measurement signals 62 of multiple representative patients P. The average value is obtained by adding the measurement signals 62 for each unit depth of multiple representative patients P and dividing by the number of patients P. The average value is an example of a "representative value" related to the technology of this disclosure. Note that the median, mode, etc. may also be used as representative values.

[0105] Furthermore, the reference signal 60 may be estimated based on a theoretical model. When estimated based on a theoretical model, the reference signal 60 may be generated based on the transmit beam profile and the gain profile. The simplest method is to generate the reference signal 60 by adding the transmit beam profile and the gain profile, as shown in Figure 27 as an example. The transmit beam profile is beamforming data dependent on the transmit focus position extracted from the measured signal 62. The gain profile is beamforming data with gain correction.

[0106] In each of the above embodiments, the processing of each processing unit, such as the image generation unit 33, signal acquisition unit 65, instruction reception unit 66, selection unit 67, setting unit 68, calculation unit 69, and detection unit 80, is executed on any computer. Furthermore, any computer may execute these processes using a processor as hardware, a program as software, or a combination thereof. In this case, the processor is configured to work in cooperation with the program to execute the various processes in each of the above embodiments, and can function as each unit or means in each of the above embodiments. Also, the execution order of the processes by the processor is not limited to the order described and may be changed as appropriate. Any computer may be a general-purpose computer, a computer designed for a specific application, a workstation, or any other system capable of executing each of the processes.

[0107] A processor may consist of one or more hardware components, and the type of hardware is not limited. For example, a processor may consist of the example CPU 51, or programmable logic devices such as an MPU (Micro Processing Unit), FPGA (Field Programmable Gate Array), dedicated circuits for executing specific processes such as an ASIC (Application Specific Integrated Circuit), a GPU (Graphic Processing Unit), or an NPU (Neural Processing Unit). Furthermore, the type of hardware may be a combination of different types of hardware. When multiple hardware components are configured to execute one or more processes of a given processor, these multiple hardware components may reside in physically separate devices or in the same device. Also, in any embodiment, the order of each process performed by the processor is not limited to the order described above and may be changed as appropriate. The hardware is composed of electrical circuits (circuitry) that combine circuit elements such as semiconductor elements.

[0108] Furthermore, the program may be firmware or software such as microcode. Alternatively, the program may be, for example, a set of program modules, each function of which may be implemented by a processor configured to perform its respective function. The program may be program code or multiple code segments stored on one or more non-temporary computer-readable media (e.g., storage media or other storage devices). The program may be divided and stored on multiple non-temporary computer-readable media located in physically separate devices. Program code or code segments may represent any combination of procedures, functions, subprograms, routines, subroutines, modules, software packages, classes, or instructions, data structures, or program statements. Program code or code segments may be connected to other code segments or hardware circuits by sending and receiving information, data, arguments, parameters, or memory contents.

[0109] From the above description, the technology described in the following supplementary information can be understood.

[0110] [Additional note 1] Equipped with a processor, The aforementioned processor, Select a reference signal from among multiple reference signals according to the measurement conditions. Based on the measurement signal obtained by measuring the subject and the selected reference signal, the attenuation rate of the measurement signal is calculated. Ultrasound diagnostic equipment. [Additional note 2] The ultrasound diagnostic apparatus according to Appendix 1, wherein the measurement conditions are at least one of the measurement area, the focus position of the transmitted wave, the gain applied to the echo signal, the frequency of the transmitted wave, the type of probe, and the organ to be measured. [Additional note 3] The ultrasound diagnostic apparatus according to Appendix 1, wherein the measurement conditions are at least one of the measurement area, the focus position of the transmitted wave, the gain applied to the echo signal, and the frequency of the transmitted wave. [Additional note 4] The aforementioned processor, The measurement target area that satisfies the detection conditions is detected, An ultrasound diagnostic apparatus according to Appendix 2 or Appendix 3, which selects a reference signal corresponding to the detected measurement target area. [Additional note 5] The ultrasound diagnostic apparatus described in Appendix 4, wherein the detection conditions include conditions relating to the distance to the organ to be measured and conditions relating to the intensity of the echo signal. [Additional note 6] The ultrasound diagnostic apparatus described in Appendix 2, wherein the type of probe is either a probe for use on the body surface or a probe for insertion into the body. [Additional note 7] The ultrasound diagnostic device described in Appendix 2, wherein the organ to be measured is either the liver or the pancreas. [Additional note 8] An ultrasonic diagnostic apparatus according to any one of the appendix items 1 to 7, wherein the calculation result information of the attenuation rate is displayed on the display unit. [Additional note 9] The calculation result information is a color map representing the level of the attenuation rate in colors, as described in Appendix 8 of the ultrasound diagnostic apparatus. [Additional Note 10] The ultrasonic diagnostic apparatus according to Appendix 8 or Appendix 9, wherein the reference signal used to calculate the attenuation rate is displayed on the display unit together with the calculation result information. [Additional Note 11] The ultrasound diagnostic apparatus according to any one of the appendix items 1 to 10, wherein the reference signal is one of the following: a measurement signal obtained using a phantom, a representative value of the measurement signals of multiple representative subjects, or a measurement signal obtained using a phantom corrected with the representative value of the measurement signals of multiple representative subjects. [Additional Note 12] The ultrasound diagnostic apparatus according to any one of the appendices 1 to 10, wherein the reference signal is generated based on the transmit beam profile and the gain profile.

[0111] The technology of this disclosure can be appropriately combined with the various embodiments and / or variations described above. Furthermore, it is understood that various configurations can be adopted without departing from the spirit of the invention, and the invention is not limited to the embodiments described above. In addition, the technology of this disclosure extends not only to programs, but also to storage media for non-temporarily storing programs, and to computer program products containing programs.

[0112] The descriptions and illustrations presented above are detailed explanations of the technical aspects of this disclosure and are merely examples of the technical aspects. For example, the above descriptions of the structure, function, operation, and effect are examples of the structure, function, operation, and effect of the technical aspects of this disclosure. Therefore, it goes without saying that you may delete unnecessary parts, add new elements, or replace elements in the descriptions and illustrations presented above, as long as you do not deviate from the essence of the technical aspects of this disclosure. Furthermore, in order to avoid confusion and facilitate understanding of the technical aspects of this disclosure, explanations of common technical knowledge and the like that do not require special explanation to enable the implementation of the technical aspects of this disclosure have been omitted from the descriptions and illustrations presented above.

[0113] In this specification, "A and / or B" is synonymous with "at least one of A and B." That is, "A and / or B" means that it may be A alone, or B alone, or a combination of A and B. Furthermore, in this specification, the same concept as "A and / or B" applies when expressing three or more things linked by "and / or."

[0114] All documents, patent applications, and technical standards described herein are incorporated by reference to the same extent as if each individual document, patent application, and technical standard were specifically and individually noted to be incorporated by reference. [Explanation of symbols]

[0115] 10. Ultrasound diagnostic equipment 11.90 Main unit of the device 12 Surface probes 13 displays 14 Input Devices 15 Cables 16 berths 17, 94 B-mode images 18 carts 19 wheels 25, 93 transducer array 26 Transducers 30 Multiplexer 31 Transmitter 32 Receiver 33 Image generation unit 34 Control Unit 35 Transmitting pulse generator 36. Transmit delay circuit 37 Parsa 38 Analog Front-End Circuits 39 Beamforming Circuit 40 Low-noise amplifier (LNA) 41. Time Gain Correction Amplifier (TGC) 42. Aliasing Noise Prevention Filter (AAF) 43. Analog-to-Digital Converter (ADC) 50 storage 51 CPU 52 memory 53 Bus Line 55 Operating Program 56. Reference Signal Database (Reference Signal DB) 57 Configuration Information Table 60 Reference signal 61 Dashed line indicating the measurement area 62 Measurement signal 63. Configuration Information 65 Signal acquisition unit 66 Instruction Reception Department 67 Selection Section 68 Settings Section 69 Calculation Section Change instructions for 70, 85, 87, 89, and 110. 71 Calculation Results 75 Diagnostic screen 76 Basic measurement information 77 Graphs 80 Detection unit 81 Detection conditions 82 Detection Results 91 Probe for internal insertion 92 Insertion section 100, 105 Specification table 115 Color Map 116 Color Bars E esophagus HV (Hepatic Vein) L straight line Li Liver OP Operator P patient pancreas PH Phantom RU reflected wave St stomach ST100, ST110, ST120, ST130, ST140, ST150, ST160 Step TU transmit wave

Claims

1. Equipped with a processor, The aforementioned processor, Select a reference signal from among multiple reference signals according to the measurement conditions. Based on the measurement signal obtained by measuring the subject and the selected reference signal, the attenuation rate of the measurement signal is calculated. Ultrasound diagnostic equipment.

2. The ultrasound diagnostic apparatus according to claim 1, wherein the measurement conditions are at least one of the measurement area, the focus position of the transmitted wave, the gain applied to the echo signal, the frequency of the transmitted wave, the type of probe, and the organ to be measured.

3. The ultrasonic diagnostic apparatus according to claim 1, wherein the measurement conditions are at least one of the measurement target area, the focus position of the transmitted wave, the gain applied to the echo signal, and the frequency of the transmitted wave.

4. The aforementioned processor, The measurement target area that satisfies the detection conditions is detected, The ultrasonic diagnostic apparatus according to claim 2, which selects a reference signal corresponding to the detected measurement target area.

5. The ultrasound diagnostic apparatus according to claim 4, wherein the detection conditions include conditions relating to the distance to the organ to be measured and conditions relating to the intensity of the echo signal.

6. The ultrasound diagnostic apparatus according to claim 2, wherein the type of probe is either a probe for use on the body surface or a probe for insertion into the body.

7. The ultrasound diagnostic device according to claim 2, wherein the organ to be measured is either the liver or the pancreas.

8. The ultrasonic diagnostic apparatus according to claim 1, wherein the calculation result information of the attenuation rate is displayed on the display unit.

9. The ultrasonic diagnostic apparatus according to claim 8, wherein the calculation result information is a color map representing the level of the attenuation rate in colors.

10. The ultrasonic diagnostic apparatus according to claim 8, wherein the reference signal used to calculate the attenuation rate is displayed on the display unit together with the calculation result information.

11. The ultrasound diagnostic apparatus according to claim 1, wherein the reference signal is one of the following: a measurement signal obtained using a phantom, a representative value of the measurement signals of a plurality of representative subjects, or a measurement signal obtained using a phantom corrected with the representative value of the measurement signals of a plurality of representative subjects.

12. The ultrasonic diagnostic apparatus according to claim 1, wherein the reference signal is generated based on the transmit beam profile and the gain profile.

13. Selecting a reference signal from among multiple reference signals according to the measurement conditions, and, The attenuation rate of the measurement signal is calculated based on the measurement signal obtained by measuring the subject and the selected reference signal. A method for operating an ultrasound diagnostic device, including the device itself.

14. Selecting a reference signal from among multiple reference signals according to the measurement conditions, and, The attenuation rate of the measurement signal is calculated based on the measurement signal obtained by measuring the subject and the selected reference signal. An operating program for an ultrasound diagnostic device that causes a computer to perform a process including [specific actions].

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