JP6589619B2 - Ultrasonic diagnostic equipment - Google Patents

Description

  The present invention relates to an ultrasonic diagnostic apparatus.

  2. Description of the Related Art Conventionally, there is an ultrasonic diagnostic apparatus that inspects an internal structure of a subject by irradiating the subject with ultrasonic waves, receiving a reflected wave (echo) inside the subject, and performing predetermined signal data processing. is there. Such an ultrasonic diagnostic apparatus is widely used for various purposes such as medical purpose inspection, treatment, and inspection inside a building structure.

  The ultrasonic diagnostic apparatus not only displays the image by processing the acquired reflected wave data, but also collects a sample of a specific part (target) in the subject, discharges water or the like, or Also, when a drug or marker is injected or placed at a specific site, it is also used when the puncture needle is inserted toward the target position while visually checking the puncture needle used for these and the position of the target. It is done. By using such an ultrasonic image, it is possible to quickly, surely and easily perform a treatment on a target in a subject.

  However, since the puncture needle is usually inserted thinly and obliquely with respect to the subject, the reflected ultrasonic wave incident perpendicularly to the subject is not sufficiently reflected in the transmission / reception direction of the ultrasonic wave. Therefore, there is a problem that it does not appear clearly in the ultrasonic image and is difficult for the user to visually recognize.

  On the other hand, conventionally, there are various techniques for allowing the user to visually recognize the puncture needle more clearly. As one of these techniques, there is a technique for analyzing an ultrasonic image to detect a puncture needle and highlight it. Patent Document 1 relates to a technique for performing enhancement processing of a puncture needle by acquiring information related to the insertion direction of the puncture needle and applying a filter that emphasizes an edge of luminance extending in the insertion direction in an ultrasonic image. It is disclosed. In Patent Document 2, the position of the puncture needle is specified by detecting a high-luminance region that appears linearly from the ultrasound image and specifying the tip of the puncture needle based on the luminance distribution on the straight line. Technology is disclosed.

Japanese Patent No. 5473853 Japanese Patent No. 5486449

  However, in order to acquire information such as the insertion accuracy of the puncture needle, there is a problem that an additional configuration and labor are required in addition to the conventional configuration. Further, the conventional detection technique has a problem that it is easy to detect other existing linear luminance distributions.

  An object of the present invention is to provide an ultrasonic diagnostic apparatus that can easily and more accurately detect a puncture needle.

In order to solve the above-mentioned problem, the invention described in claim 1
An ultrasound diagnostic apparatus that generates an ultrasound image inside a subject based on an ultrasound signal reflected and received inside the subject,
For each region defined by one or a plurality of pixels in the ultrasound image, the distribution of the ultrasound signal along the incident direction of the ultrasound incident on the subject is deeper than the region to be determined A needle position determination unit that acquires a depth feature value related to signal intensity in a region, and determines a position of a puncture needle inserted into the subject based on the depth feature value;
A needle emphasis processing unit that performs processing for emphasizing the position of the puncture needle determined in the ultrasound image;
It is characterized by having.

The invention according to claim 2 is the ultrasonic diagnostic apparatus according to claim 1,
The needle position determination unit determines a position of the puncture needle based on the predetermined feature amount, with a value related to the rate of change of the depth feature value in the incident direction as the predetermined feature amount. .

The invention described in claim 3 is the ultrasonic diagnostic apparatus according to claim 1,
The needle position determination unit obtains the deep feature value and a shallow feature value related to signal intensity in a region shallower than the determination target region, and based on the deep feature value and the shallow feature value, The position of the puncture needle inserted into the subject is determined.

According to a fourth aspect of the present invention, in the ultrasonic diagnostic apparatus according to the third aspect,
The needle position determination unit uses a product of a value related to the rate of change of the depth feature value in the incident direction and the shallow feature value as a predetermined feature amount, and based on the predetermined feature amount, The position is determined.

Further, the invention according to claim 5 is the ultrasonic diagnostic apparatus according to claim 3,
The needle position determination unit uses the sum of a value relating to the rate of change of the depth feature value in the incident direction and a value obtained by multiplying the shallow feature value by a predetermined coefficient as the predetermined feature value. The position of the puncture needle inserted into the subject is determined based on the above.

The invention according to claim 6 is the ultrasonic diagnostic apparatus according to claim 3,
The needle position determination unit determines a position of the puncture needle inserted into the subject based on the predetermined feature amount, using a difference between the deep portion feature value and the shallow portion feature value as a predetermined feature amount. It is characterized by doing.

The invention according to claim 7 is the ultrasonic diagnostic apparatus according to claim 6,
The needle position determination unit determines the position of a puncture needle inserted into the subject based on a value related to a rate of change of the predetermined feature amount in the incident direction.

The invention according to claim 8 is the ultrasonic diagnostic apparatus according to any one of claims 3 to 7,
The needle position determination unit acquires, as the shallow portion characteristic value, any one of an average value, a mode value, and a median value corresponding to the signal intensity in each region in a direction shallower than the determination target region. It is characterized by that.

The invention according to claim 9 is the ultrasonic diagnostic apparatus according to any one of claims 1 to 8,
The needle position determination unit is characterized in that a maximum value of a value corresponding to a signal intensity in each region deeper than the determination target region is acquired as the deep feature value.

The invention described in claim 10 is the ultrasonic diagnostic apparatus according to any one of claims 2, 4-7,
The needle position determining unit extracts a plurality of the regions where the predetermined feature amount satisfies a predetermined condition as detection candidate regions, and determines the position of the puncture needle based on the detection candidate regions. .

The invention according to claim 11 is the ultrasonic diagnostic apparatus according to claim 10,
The plurality of detection candidate regions are set in units of pixels of the ultrasonic image.

The invention according to claim 12 is the ultrasonic diagnostic apparatus according to any one of claims 1 to 11,
A transmitter / receiver for transmitting / receiving the ultrasonic signal;
A transmission / reception control unit for controlling a transmission / reception range by the transmission / reception unit;
With
The transmission / reception control unit is configured to acquire the puncture when acquiring an ultrasonic image for determining the position of the puncture needle by the needle position determination unit rather than acquiring an ultrasonic image without determining the position of the puncture needle. The width in which the ultrasonic waves are incident in the width direction perpendicular to the length direction of the needle is narrowed.

The invention according to claim 13 is the ultrasonic diagnostic apparatus according to any one of claims 1 to 12,
The determined shape of the puncture needle is a linear shape.

  According to the present invention, there is an effect that the puncture needle can be detected easily and more accurately in the ultrasonic diagnostic apparatus.

1 is an overall configuration diagram of an ultrasonic diagnostic apparatus according to an embodiment of the present invention. It is a block diagram which shows the internal structure of an ultrasonic diagnosing device. It is a schematic diagram for demonstrating calculation of the detection map data which concern on a puncture needle detection. It is a figure which shows the example of calculation of puncture needle detection map data. It is a figure which shows the example which detected the straight line corresponding to a puncture needle based on a detection map data map. It is a figure for demonstrating the emphasis process of a puncture needle. It is a figure which shows an example which concerns on estimation of the front-end | tip position of a puncture needle. It is a figure which shows the 2nd example which concerns on estimation of the front-end | tip position of a puncture needle. It is a figure which shows the 3rd example which concerns on estimation of the front-end | tip position of a puncture needle. It is a figure which shows the 4th example which concerns on estimation of the front-end | tip position of a puncture needle. It is a figure which shows the example of a highlight display of the position of the identified puncture needle. It is a flowchart which shows the control procedure of a puncture needle detection emphasis process. It is a schematic diagram which shows the example of a change of the shallow part characteristic value with respect to a depth direction, a deep part characteristic value, a feature-value, and a partial differential value. It is a schematic diagram which shows the example of the change of the feature-value calculated | required with the shallow part characteristic value with respect to a depth direction, a deep part characteristic value, a partial differential value, and the ultrasonic diagnostic apparatus of 2nd Embodiment.

Hereinafter, embodiments of the present invention will be described with reference to the drawings.
[First Embodiment]
First, a first embodiment of the ultrasonic diagnostic apparatus of the present invention will be described.
FIG. 1 is an overall view of an ultrasonic diagnostic apparatus U according to the first embodiment. FIG. 2 is a block diagram showing an internal configuration of the ultrasonic diagnostic apparatus U. As shown in FIG.

  As shown in FIG. 1, the ultrasonic diagnostic apparatus U includes an ultrasonic diagnostic apparatus main body 1 and an ultrasonic probe 2 (ultrasonic probe, transmission / reception) connected to the ultrasonic diagnostic apparatus main body 1 via a cable 22. Part), an attachment part 4 (attachment, insertion mechanism) attached to the ultrasonic probe 2, a puncture needle 3, and the like.

  Here, the puncture needle 3 has a hollow long needle shape, and is inserted into the subject at an angle determined by the setting of the attachment portion 4. The puncture needle 3 can be replaced with one having an appropriate thickness, length, and tip shape according to the type and quantity of the collection target (sample) or the medicine to be injected.

  The attaching part 4 holds the puncture needle 3 in a set direction (direction). The attachment portion 4 is attached to the side portion of the ultrasonic probe 2 and can change and set the direction of the puncture needle 3 according to the insertion angle of the puncture needle 3 with respect to the subject. Instead of the attachment portion 4, the ultrasonic probe 2 may be directly provided with a guide portion for holding the puncture needle 3 in the insertion direction.

The ultrasonic diagnostic apparatus main body 1 is provided with an operation input unit 18 and an output display unit 19. Further, as shown in FIG. 2, in addition to these, the ultrasonic diagnostic apparatus body 1 includes a control unit 11 (transmission / reception control unit), a transmission drive unit 12, a reception drive unit 13, a transmission / reception switching unit 14, An image generation unit 15 and an image processing unit 16 are provided.
The control unit 11 of the ultrasonic diagnostic apparatus main body 1 uses an operation signal from an input device such as a keyboard or a mouse of the operation input unit 18 by an input operation from the outside or a detection signal from a touch sensor that detects a contact operation to the display screen. Based on this, a drive signal is output to the ultrasonic probe 2 to output an ultrasonic wave, and a reception signal related to ultrasonic reception is acquired from the ultrasonic probe 2 and various processes are performed. A series of operations for displaying results on the display screen of the output display unit 19 is performed.

The control unit 11 includes a central processing unit (CPU), a hard disk drive (HDD), a random access memory (RAM), and the like. The CPU reads out various programs stored in the HDD, loads them into the RAM, and performs overall control of operations of the respective units of the ultrasonic diagnostic apparatus U according to the programs. The HDD stores a control program and various processing programs for operating the ultrasonic diagnostic apparatus U, various setting data, and the like. These programs and setting data may be stored in an auxiliary storage device using a nonvolatile memory such as a flash memory including an SSD (Solid State Drive) in addition to the HDD so as to be able to be read / written and updated. The RAM is a volatile memory such as SRAM or DRAM, provides a working memory space for the CPU, and stores temporary data.

  The transmission drive unit 12 outputs a pulse signal to be supplied to the ultrasonic probe 2 in accordance with a control signal input from the control unit 11, and causes the ultrasonic probe 2 to generate an ultrasonic wave. The transmission drive unit 12 includes, for example, a clock generation circuit, a pulse generation circuit, a pulse width setting unit, and a delay circuit. The clock generation circuit is a circuit that generates a clock signal that determines the transmission timing and transmission frequency of the pulse signal. The pulse width setting unit sets the waveform (shape), voltage amplitude, and pulse width of the transmission pulse output from the pulse generation circuit. The pulse generation circuit generates a transmission pulse based on the setting of the pulse width setting unit, and outputs the transmission pulse to a different wiring path for each transducer 210 of the ultrasonic probe 2. The delay circuit counts the clock signal output from the clock generation circuit, and when the set delay time elapses, the delay circuit generates a transmission pulse and outputs it to each wiring path.

  The reception driving unit 13 is a circuit that acquires a reception signal input from the ultrasound probe 2 according to the control of the control unit 11. The reception drive unit 13 includes, for example, an amplifier, an A / D conversion circuit, and a phasing addition circuit. The amplifier is a circuit that amplifies a reception signal corresponding to the ultrasonic wave received by each transducer 210 of the ultrasonic probe 2 with a predetermined amplification factor set in advance. The A / D conversion circuit is a circuit that converts an amplified received signal into digital data at a predetermined sampling frequency. The phasing addition circuit adjusts the time phase by giving a delay time to each wiring path corresponding to each transducer 210 with respect to the A / D converted received signal, and adds these (phasing addition) to generate a sound. A circuit for generating line data.

  Based on the control of the control unit 11, the transmission / reception switching unit 14 transmits a drive signal from the transmission drive unit 12 to the transducer 210 when the ultrasonic wave is emitted (transmitted) from the transducer 210, while the transducer 210 emits it. When a signal related to the ultrasonic wave is acquired, a switching operation for causing the reception driving unit 13 to output the reception signal is performed.

  The image generation unit 15 generates a diagnostic image (ultrasonic image) based on ultrasonic reception data (ultrasonic signal). The image generation unit 15 detects signals (envelope detection) from the sound ray data input from the reception driving unit 13 and acquires signals, and also performs logarithmic amplification and filtering (for example, low-pass processing, smoothing) as necessary. Etc.) and emphasis processing. As one of the diagnostic images, the image generation unit 15 transmits an ultrasonic wave transmitted by the ultrasonic probe 2 and a signal transmission direction (incident direction, depth direction of the subject) with a luminance signal corresponding to the signal intensity. Each frame image data related to the B mode display representing a two-dimensional structure in the plane including the scanning direction (structure inside the subject) is generated. At this time, the image generation unit 15 can perform dynamic range adjustment and gamma correction related to display. The image generation unit 15 can be configured to include a dedicated CPU and RAM used for generating these images. Alternatively, the image generation unit 15 may be provided with a dedicated hardware configuration for image generation formed on a substrate (such as an ASIC (Application-Specific Integrated Circuit)). Alternatively, the image generation unit 15 may have a configuration in which processing related to image generation is performed by the CPU and RAM of the control unit 11.

The image processing unit 16 performs various processes for detecting and highlighting the puncture needle 3 from the generated diagnostic image, and temporarily stores and holds it until the display timing. The image processing unit 16 includes a storage unit 161, a detection map generation unit 162, a puncture needle identification unit 163, an enhancement processing unit 164 (needle enhancement processing unit), and the like.
The detection map generation unit 162 and the puncture needle identification unit 163 constitute a needle position determination unit.

  The storage unit 161 stores diagnostic image data (frame image data) processed by the image generation unit 15 and used for real-time display or display conforming thereto for a predetermined number of frames in a frame unit. The storage unit 161 is, for example, a volatile memory such as a DRAM (Dynamic Random Access Memory). Alternatively, the storage unit 161 may be a nonvolatile memory that can be rewritten at high speed. The diagnostic image data stored in the storage unit 161 is read according to the control of the control unit 11 and transmitted to the output display unit 19 or output to the outside of the ultrasound diagnostic apparatus U via a communication unit (not shown). Or At this time, when the display system of the output display unit 19 is a television system, a DSC (Digital Signal Converter) is provided between the storage unit 161 and the output display unit 19 to output after the scanning format is converted. It should be done. In addition, the storage unit 161 is preset with diagnostic image data for which a storage command has been issued in response to an input operation to the operation input unit 18 by a user of the ultrasonic diagnostic apparatus U during the operation of the ultrasonic diagnostic apparatus U. It can be stored for a certain period or until it is erased by a user input operation.

  The detection map generation unit 162 generates detection map data for identifying the puncture needle 3 by the puncture needle identification unit 163 and determining its position. The detection map data will be described in detail later.

  The puncture needle identification unit 163 identifies the puncture needle 3 using the detection map data generated by the detection map generation unit 162. The puncture needle identification unit 163 stores a history of puncture needle positions identified so far, and can calculate, for example, the change speed and change direction (displacement vector) of the position. In this case, the puncture needle identification unit 163 obtains an estimated position of the next puncture needle 3 based on the position and change vector of the puncture needle 3 and can use it for identification.

  The enhancement processing unit 164 performs processing for enhancing the position of the identified puncture needle 3 on the display image. The enhancement processing unit 164 determines the content of the enhancement processing according to the position of the puncture needle 3 and the accuracy of identification identified and determined by the puncture needle identification unit 163, performs the enhancement processing on the diagnostic image, and stores the storage unit. 161 is stored.

  The detection map generation unit 162, the puncture needle identification unit 163, and the enhancement processing unit 164 may use the CPU and RAM of the image processing unit 16 in common, or may each include a dedicated CPU and RAM. Alternatively, the detection map generation unit 162, the puncture needle identification unit 163, and the enhancement processing unit 164 may be subjected to various processes by the CPU and RAM of the control unit 11.

  The operation input unit 18 includes a push button switch, a keyboard, a mouse, a track ball, a touch sensor for a display screen, or a combination thereof. The operation input unit 18 converts a user's input operation into an operation signal. To enter.

The output display unit 19 is a display using any one of various display methods such as an LCD (Liquid Crystal Display), an organic EL (Electro-Luminescent) display, an inorganic EL display, a plasma display, and a CRT (Cathode Ray Tube) display. A screen and its drive unit are provided. The output display unit 19 generates a drive signal for the display screen (each display pixel) in accordance with the control signal output from the CPU 15 and the image data generated by the image processing unit 16, and a menu related to ultrasonic diagnosis on the display screen. , Display the status and measurement data based on the received ultrasound. In addition, the output display unit 19 may have a configuration in which an LED lamp or the like is separately provided to display whether or not the power is turned on.

  The operation input unit 18 and the output display unit 19 may be provided integrally with the casing of the ultrasonic diagnostic apparatus main body 1, or may be an RGB cable, a USB cable, or an HDMI cable (registered trademark: HDMI) or the like may be attached to the outside. Further, if the operation input terminal and the display output terminal are provided in the ultrasonic diagnostic apparatus main body 1, conventional peripheral devices for operation and display may be connected to these terminals for use.

  The ultrasonic probe 2 oscillates an ultrasonic wave (here, about 1 to 30 MHz) and emits it to a subject such as a living body, and a reflected wave (reflected by the subject) of the emitted ultrasonic wave ( It functions as an acoustic sensor that receives (echo) and converts it into an electrical signal. The ultrasonic probe 2 includes a transducer array 21 (transmission / reception unit) that is an array of a plurality of transducers 210 that transmit and receive ultrasonic waves, a cable 22, and the like.

The cable 22 has a connector (not shown) to the ultrasonic diagnostic apparatus main body 1 at one end, and the ultrasonic probe 2 is configured to be detachable from the ultrasonic diagnostic apparatus main body 1 by the cable 22. ing. The user operates the ultrasound diagnostic apparatus U by bringing the ultrasound transmitting / receiving surface of the ultrasound probe 2 into contact with the subject with a predetermined pressure, that is, the surface in the direction in which the ultrasound is emitted from the transducer array 21. And perform an ultrasound diagnosis.
The ultrasonic diagnostic apparatus main body 1 and the ultrasonic probe 2 can be connected not only by the wired cable 22 but also by wireless communication means using infrared rays, radio waves, or the like.

  The vibrator array 21 is an array of a plurality of vibrators 210 including piezoelectric elements each having a piezoelectric body and electrodes provided at both ends where charges appear due to deformation (extension / contraction) thereof, for example, in a predetermined direction (scanning direction). Is a one-dimensional array. By sequentially supplying voltage pulses (pulse signals) to the vibrator 210, the piezoelectric bodies are deformed according to the electric field generated in each piezoelectric body, and ultrasonic waves are transmitted. Further, when an ultrasonic wave having a predetermined frequency band is incident on the vibrator 210, the thickness of the piezoelectric body fluctuates (vibrates) due to the sound pressure, thereby generating a charge corresponding to the fluctuation amount. Converted to electrical signal and output.

Next, a method for detecting the puncture needle 3 in the ultrasonic diagnostic apparatus U of the present embodiment will be described in detail.
FIG. 3 is a schematic diagram for explaining calculation of detection map data related to puncture needle detection. FIG. 4 is a diagram illustrating a calculation example of puncture needle detection map data.
Here, an ultrasonic wave is incident downward (z direction) from the ultrasonic probe 2 in the upper part of the figure, and a reflected wave that is reflected inside the subject Q and transmitted upward is received and detected.

The puncture needle 3 has a large amount of ultrasonic components reflected in a direction different from the upper direction (in FIG. 3, diagonally upward to the right) due to its thickness and inclination, and has a small component that propagates directly downward. As a result, the puncture needle 3 The lower region Q1 becomes an ultrasonic shadow region (acoustic shadow), and the ultrasonic component reflected by the region Q1 is reduced as a whole compared to the other regions Q0. Therefore, in the ultrasonic diagnostic apparatus U of the present embodiment, the puncture needle 3 is detected by identifying the boundary between the region Q0 and the region Q1.
At this time, if the ultrasonic wave travels on both sides of the puncture needle 3 (perpendicular (front-rear) direction with respect to the display surface in FIG. 3), the decrease in reflected wave intensity below becomes relatively small. It is desirable that is not too wide compared to the width of the puncture needle 3.

  In order to identify this boundary, first, for the luminance value s (x0, z0) (x0, z0 is an integer of 0 or more) corresponding to the reflected wave intensity at each pixel position (for example, (x0, z0)), An analysis is performed on the pixel position (determination target region) based on the distribution of luminance values along the incident direction (z direction) of ultrasonic waves. Here, a statistical representative value of the reflected wave intensity acquired at each pixel position on the shallower side (z ≦ z0) of the subject Q than the pixel position (x0, z0), here, the average value sa = Σs ( x0, z ≦ z0) / (z0 + 1) (shallow feature value) is calculated. The average value sa temporarily increases at each pixel position shallower than the above-described boundary position (side where z is small) as the high luminance region is included, and the deep side (side where z is large). In each pixel position of (), it gradually decreases as the ratio of the area with low overall luminance increases. Further, at the position where the puncture needle 3 is not inserted, there is no decrease in the overall density, so the value of the average value sa does not change greatly. Alternatively, other statistical values representing pixel values on the shallow side of the subject Q, for example, the median value median (s (x0, z ≦ z0)) or the number of appearances of luminance (appearance rate) for each predetermined luminance value width g The mode value smode (s (x0, z ≦ z0), g) (its median luminance value width) in the distribution may be calculated and used as the shallow feature value.

  On the other hand, at each pixel position (x0, z0), the maximum value sm = max (s (x0, z0)) of the reflected wave intensity obtained at each pixel position on the deeper side of the subject Q (z ≧ z0) than the pixel position. z ≧ z0)) (depth feature value). When there is a high brightness point at a shallow position of the subject Q, the maximum value sm decreases discontinuously with the high brightness point as a boundary as the coordinate z0 in the depth direction increases. In the position of the puncture needle 3, this discontinuous drop occurs with a high probability.

Therefore, at each pixel position (x0, z0), the feature value sc = sa−sm, which is the difference between the average value sa and the maximum value sm, increases as s0 increases and sm decreases at the position of the puncture needle 3. Value. Further, the partial differential value (difference value with the adjacent pixel position) of the feature quantity sc in the z direction ds (x0, z0) = ∂s / ∂z, here, for example, simply sc (x0, z0) − sc (x0, z0-1) is calculated for each x0, z0, and is used as detection map data.
With respect to the diagnostic image of FIG. 4A, a two-dimensional map of the feature quantity sc is obtained as shown in FIG. 4B, and detection map data is obtained as shown in FIG. 4C. .

  Once the partial differential values ds are obtained for all pixel positions, the puncture needle 3 is detected using the detection map data. For this detection, a conventionally known detection method, in particular, a method for detecting a straight line from image data is used. Here, for example, Hough conversion is used.

  FIG. 5 is a diagram illustrating an example in which a straight line corresponding to the puncture needle 3 is detected based on the detection map data obtained in FIG.

  The partial differential value ds that is the value of each point on the detection map data obtained in FIG. 4C is binarized with a predetermined threshold, for example, and is equal to or greater than the threshold as shown in FIG. A point (which satisfies a predetermined condition) is determined as a candidate point (xi, zi) (a pixel in a detection candidate region) of the puncture needle 3. The candidate point (xi, zi) cannot normally clearly indicate a range (needle position range) corresponding to the entire position of the puncture needle 3 in the ultrasonic image, and is often determined discretely.

Next, in consideration of the fact that the puncture needle 3 has a linear shape, detection of the straight line in which the candidate points are densely arranged on the same straight line according to the shape of the puncture needle 3 is performed by Hough transform (FIG. 5 (b)). When each candidate point (xi, zi) is represented by ρ = xi · cos θ + zi · sin θ using the length variable ρ and the angle variable θ, the combination of (ρ, θ) satisfying this expression is the candidate point (xi , Zi) represents the length of the perpendicular from the origin to the straight line passing through, and the angle formed by the x-axis and the straight line. Therefore, the points (ρ0, θ0) with votes from the largest number of candidate points (xi, zi) represent likely straight lines (candidate lines) that pass on these candidate points (FIG. 5C). .
As a technique for detecting a line segment instead of a straight line, there is a stochastic Hough transform. In this probabilistic Hough transform, candidate lines are detected from a randomly selected point group by Hough transform, and then the existence range of the selected point group on the candidate line is confirmed. Thus, by defining the start point and the end point on the candidate line, it is possible to detect the line segment (length) as a result.

  At this time, when there are candidate points arranged in a straight line other than the puncture needle 3, it is not always necessary to narrow down to one candidate line, and a plurality of candidate lines may be left. In addition, when the position of the puncture needle 3 can be estimated in advance based on another method, a candidate line by the puncture needle 3 may be selected from a plurality based on the estimation.

  When a candidate line is detected, the degree of enhancement of the candidate line is determined according to the certainty of the candidate line (FIG. 5D). That is, even when a plurality of candidate lines remain, the degree of emphasis can be changed between a low possibility and a high possibility that the puncture needle 3 is applicable.

Next, highlighting of the puncture needle 3 in the diagnostic image will be described.
In the ultrasonic diagnostic apparatus U according to the present embodiment, for a range in which the puncture needle 3 is likely to exist on the candidate line selected for the diagnostic image, highlighting is performed on the diagnostic image with an emphasis degree according to the likelihood. On the other hand, the puncture needle 3 is highlighted by overlapping.

FIG. 6 is a diagram for explaining the emphasis process of the puncture needle 3.
As described above, since both ends of the candidate line L selected using the Hough transform are not determined, the tip position of the puncture needle 3 cannot be specified. In addition, the distal end portion of the puncture needle 3 is more difficult to identify because the ultrasonic wave scatters more and the reflected waves are smaller than other portions of the puncture needle 3 due to its shape and the like. Also, when there is noise or other structure that reflects ultrasonic waves at the tip of the tip, the position is misrecognized as the tip and the highlighting is different from the accurate range. May end up. Therefore, in the ultrasonic diagnostic apparatus U of the present embodiment, a plausible puncture needle based on the distribution state of candidate points used for selecting the candidate line L, particularly the state of the set (the center position of the set, the degree of set, etc.) In the range of 3, highlighting (emphasis suppression) is performed while changing the degree of emphasis.

  In the diagram shown in FIG. 6, the candidate points schematically indicated by circles (◯) are distributed on the candidate line L so as to be biased to the left side. Further, in the vicinity of the actual tip position of the puncture needle 3 indicated by a plus sign (+), there are fewer candidate points than in the vicinity of the left end, and there are also some candidate points ahead (right side) of the tip position. Yes.

  Here, for example, first, for all candidate points (xi, zi) (1 ≦ i ≦ N) on the candidate line, the feature quantity ωi = sc (xi, zi) at each candidate point (xi, zi). Each is weighted to calculate a weighted average position (xc, zc). That is, the weighted average position (xc, zc) is obtained by using N candidate points (xi, zi) satisfying 1 ≦ i ≦ N and N feature quantities ωi, and xc = Σ (ωi · xi) / Σ. (Ωi), zc = Σ (ωi · zi) / Σ (ωi). Then, the degree of emphasis is reduced with a predetermined filter with the weighted average position as a reference. The filter is not particularly limited. For example, a window function such as a Gaussian window or a Hamming window is used. The width of the window is the length of the candidate line in the diagnostic image regardless of the actual distribution of candidate points. Alternatively, it may be determined by a variance value (standard deviation) of candidate points on the candidate line. In addition, the variance value may be calculated separately on the left side and the right side with respect to the weighted average position, or not only the variance value but also the skewness and kurtosis may be obtained and used. Also, for these window functions, appropriate ones may be selected from a plurality of lists according to the number and distribution of candidate points.

  Further, in order to more correspond to the existence range of the puncture needle 3, the extraction density of candidate points is obtained for each range of a predetermined size, and the density range is equal to or higher than a predetermined ratio compared to the density of the range including the weighted average position. On the other hand, the degree of emphasis may not be reduced. In particular, when the puncture needle 3 is included in the diagnostic image across one end of the diagnostic image, the degree of enhancement of the puncture needle 3 from the weighted average position to the end is not suppressed. It is also good. Alternatively, since the number of candidate points on the candidate line L usually increases as the existence range of the puncture needle 3 becomes longer, a range in which the degree of emphasis is not lowered is determined according to the number of candidate points, or a filter window The width may be changed.

  When the candidate point extraction range and the non-extraction range are clearly separated by this method, this boundary may be simply used as the tip of the puncture needle 3, or may be changed by another method or by another method. It is also possible to estimate the tip position using a method together and set the window width according to the length between the weighted average position and the position.

FIG. 7 is a diagram illustrating an example related to the estimation of the tip position of the puncture needle 3.
When there are two diagnostic images I (t) and I (t−1) acquired at different timings during insertion of the puncture needle 3 into a substantially stationary subject By generating the difference image D (t), only the tip portion of the moved puncture needle 3 appears as a non-zero difference value.

FIG. 8 is a diagram illustrating a second example relating to the estimation of the tip position of the puncture needle 3.
Here, the correlation map image R (t) indicating the distribution of the correlation values is obtained by calculating the correlation between the pixel values in the region of a predetermined size set in each of the diagnostic images of a plurality of frames. For example, a region of interest a (x, y, t) having a predetermined size centered on coordinates (x, y) in the diagnostic image I (t) is set for each pixel position coordinate (x, y). In addition, the region of interest b (x, y, t−1) of the same size centered on the coordinates (x, y) in the diagnostic image I (t−1) one frame before is set. A correlation coefficient r (x, y, t) (cross-correlation coefficient) is calculated using each pixel value in the regions a and b. When the puncture needle 3 moves, the tip position of the puncture needle 3 is estimated by decreasing the value of the correlation coefficient r (x, y, t) between the regions of interest a and b including the region. The

FIG. 9 is a diagram illustrating a third example relating to the estimation of the tip position of the puncture needle 3.
Here, pixel value dispersion images S (t) are calculated by calculating dispersion values of pixel values at the same pixel position in a plurality of (k + 1) times of diagnostic images I (t) to I (t−k) at different timings. Is generated. A standard deviation may be used instead of the variance value. As a result, in the path in which the puncture needle 3 has moved in these diagnostic images I (t) to I (t−k), the dispersion value increases due to a temporary change in the pixel value (luminance). Thus, the tip position of the puncture needle 3 is estimated.

FIG. 10 is a diagram illustrating a fourth example relating to the estimation of the tip position of the puncture needle 3.
Here, a distributed image SD (t) for (k + 1) frames of the difference image D (t) composed of the difference values between different frames shown in FIG. 7 is obtained. That is, the variance value of the pixel value at the same pixel position of the k difference images D (t) to D (t−k) is calculated, and the tip position of the puncture needle 3 is estimated from the position where the non-zero variance value exists. The

  When the tip position of the puncture needle 3 is estimated by these image processes, the reduction in the degree of emphasis from the above-mentioned weighted average position to the estimated tip position is suppressed, and the tip position on the side opposite to the weighted average position is suppressed. The window can be set so that the reduction of the degree of emphasis is large. For example, when the tip position is obtained with relatively high accuracy, the window function used to determine the enhancement range and the degree of enhancement may be a rectangular window or a similar one.

  FIG. 11 is a diagram showing a highlighted display example of the position of the puncture needle 3 identified by the ultrasonic diagnostic apparatus U of the present embodiment.

  As described above, the degree of emphasis determined in FIG. 5D is suppressed according to the distribution of candidate points (set state) on the candidate line L, and in the right side of the diagnostic image, FIG. As shown in FIG. 4, the highlighting is determined to be thin. Then, this highlighted display is superimposed on the original diagnostic image to generate an output image FIG. 11B. This highlighting can be performed more easily by making the hue (for example, blue) different from the color (for example, black and white display) of the original diagnostic image.

FIG. 12 is a flowchart showing a control procedure of the puncture needle detection emphasis process in the ultrasonic diagnostic apparatus U of the present embodiment.
This process is executed by the CPU of the control unit 11 or the image processing unit 16 as described above.

  When the puncture needle detection display process is started, the CPU uses the detection map generation unit 162 to calculate the feature amount of each pixel position from the two-dimensional structure image (diagnostic image) of the subject acquired in the same manner as in the normal B mode. Each sc is calculated and stored in association with the pixel position information (step S101). The CPU further processes the feature value sc to obtain a partial differential value ds and generates detection map data of the puncture needle 3 (step S102). The CPU extracts each candidate point within the range of the puncture needle 3 by comparing each value of the detection map data with a predetermined reference value.

  The CPU performs Hough transform on the extracted candidate points in the puncture needle identification unit 163 to detect a straight line (step S111). The CPU determines a candidate line that is a candidate for the puncture needle 3 from the detected straight line (step S112). At this time, the CPU specifies the tip position of the puncture needle 3 together if possible. The CPU determines an emphasis degree as a reference for emphasizing the candidate line (step S113).

  In the enhancement processing unit 164, the CPU calculates parameters related to the position, range, and enhancement degree distribution to be highlighted (step S121). CPU determines the suppression pattern of an emphasis range according to the likelihood as a range corresponding to the puncture needle 3 among candidate lines (step S122). The CPU generates an enhancement map reflecting the determined suppression pattern (step S123), and superimposes the generated enhancement map on the original diagnostic image (step S124). Then, the CPU stores the ultrasonic image in which the puncture needle 3 is emphasized in the storage unit 161 and ends the puncture needle detection enhancement process.

As described above, the ultrasonic diagnostic apparatus U of the present embodiment is an ultrasonic diagnostic apparatus U that generates an ultrasonic image inside the subject based on the ultrasonic signal reflected and received inside the subject. Thus, for each region of the ultrasound image, with respect to the distribution of the ultrasound signal along the incident direction of the ultrasound incident on the subject, the depth feature value relating to the signal intensity in the region deeper than the region to be judged Obtain a maximum value of a certain luminance and an average value of luminance, which is a shallow feature value related to signal intensity in a region shallower than the region to be judged, and subject based on these deep feature value and shallow feature value Detection map generation unit 162 and puncture needle identification unit 163 as a needle position determination unit for determining the position of puncture needle 3 inserted inside, and enhancement processing for performing processing for enhancing the needle position range in the ultrasound image Part 164.
Therefore, it is easy to determine the position of the puncture needle 3 that becomes the boundary of the shadow area by reflecting the decrease in luminance in the shadow area (acoustic shadow) generated by the puncture needle 3 with respect to the incident ultrasound. The puncture needle 3 can be detected easily and more accurately without complicating the configuration and processing contents than in the past.
Even when other structures that reflect ultrasonic waves are present, the position of the puncture needle 3 can be determined using the boundary of the shadow area at the position of the puncture needle 3 with higher accuracy than in the past.

  In addition, the detection map generation unit 162 determines the position of the puncture needle 3 inserted into the subject Q based on the feature amount sc using the difference between the shallow feature value and the deep feature value as the feature amount sc. To do. Therefore, the position of the puncture needle 3 is determined in the distribution of the ultrasonic intensity over the region where the ultrasonic wave is normally incident and the region that is a shadow of the puncture needle 3 by a simple calculation without complicating the processing. I can do it.

  The detection map generation unit 162 is inserted into the subject Q based on the partial differential value ds that is a value related to the rate of change in the depth direction of the difference between the shallow feature value and the deep feature value. The position of the puncture needle 3 is determined. Accordingly, it is possible to easily and accurately detect the jump of the feature amount sc at the shadow boundary by the puncture needle 3 and determine the position of the puncture needle 3 with high accuracy.

  In addition, the detection map generation unit 162 acquires any one of an average value, a mode value, and a median value corresponding to the signal intensity in each region in a direction shallower than the determination target region as the shallow portion feature value. To do. By making the statistical value representative of such a shallow region a shallow feature value, the processing is facilitated, and the position of the puncture needle 3 is easily determined appropriately within the entire distribution of the ultrasonic signals. I can do it.

  In addition, the detection map generation unit 162 acquires the maximum value corresponding to the signal intensity in each region deeper than the determination target region as the deep feature value. Therefore, it is possible to easily determine whether or not only the region where the decrease in ultrasonic intensity is caused by the shadow of the puncture needle 3 is represented at a position deeper than the position of the puncture needle 3 based on the deep feature value.

  In addition, the detection map generation unit 162 extracts a plurality of candidate points where the difference between the deep feature value and the shallow feature value satisfies a predetermined condition, and determines the position of the puncture needle based on the plurality of candidate points. . That is, since candidate points can be extracted easily and with higher accuracy than in the prior art, the position of the puncture needle 3 can be determined more accurately from these candidate points.

  In addition, since the plurality of candidate points are set in units of pixels of the ultrasonic image, it is possible to easily perform processing related to identification and enhancement of the puncture needle 3 with the same configuration as normal image processing. .

In addition, the control unit 11 includes a transducer array 21 that transmits and receives ultrasonic signals and a control unit 11 (CPU) that controls a transmission and reception range of the transducer array 21, and the control map 11 includes a plurality of candidates for the detection map generation unit 162. When acquiring an ultrasound image in which points are extracted and the puncture needle identification unit 163 identifies the puncture needle 3 and determines its position, an ultrasound that does not determine the position of the puncture needle 3 without extracting a plurality of candidate points The width at which the ultrasonic waves are incident in the width direction perpendicular to the length direction of the puncture needle 3 is narrower than when the image is acquired.
Therefore, only when imaging the puncture needle 3, the S / N ratio is not deteriorated by the ratio between the intensity of the ultrasonic wave propagated on both sides of the puncture needle 3 and the intensity of the ultrasonic wave blocked by the puncture needle 3. As described above, by narrowing the transmission width of the ultrasonic wave, an appropriate image in consideration of not degrading the image quality and sensitivity in normal image acquisition and the appropriate ultrasonic wave corresponding to the necessary sensitivity of the puncture needle 3 respectively. Can be output.

  In addition, since the position of the puncture needle 3 is determined with the shape of the identified puncture needle 3 as a straight line shape, by detecting the candidate points arranged linearly on the detection map based on the extracted candidate points, The puncture needle 3 can be easily identified by detecting an appropriate straight line.

[Second Embodiment]
Next, a second embodiment of the ultrasonic diagnostic apparatus of the present invention will be described.
The configuration of the ultrasonic diagnostic apparatus U according to the second embodiment is the same as that of the ultrasonic diagnostic apparatus according to the first embodiment, and the description thereof is omitted by using the same reference numerals.

Next, a method for detecting the puncture needle 3 in the ultrasonic diagnostic apparatus U according to the second embodiment will be described.
In the ultrasonic diagnostic apparatus U of the second embodiment, the position of the puncture needle 3 is identified mainly using the deep feature value.

  FIG. 13 is a schematic diagram illustrating a change example of the shallow feature value sa, the deep feature value sm, the feature value sc, and the partial differential value ds with respect to the depth direction.

  As described above, at a position deeper than the puncture needle 3, there is no portion where the reflected wave intensity is large due to the acoustic shadow. As a result, at the position deeper than the position of the puncture needle 3, the maximum feature value abruptly decreases, so that the deep feature value sm rapidly decreases. On the other hand, the shallow portion characteristic value sa gradually decreases according to the depth at a position deeper than the position of the puncture needle 3.

  Therefore, as is clear from FIG. 13, it is the deep feature value sm that greatly affects the increase of the partial differential value ds, and the partial differential value dsm in the depth direction of this deep feature value sm = こ の sm / ∂. The maximum value can also be obtained at the position of the puncture needle 3 by z = sm (x0, z0) -sm (x0, z0-1).

  However, when there is an ultrasonic reflection source Po other than the puncture needle 3, particularly when the reflection source Po is deeper than the puncture needle 3, the location where the partial differential value dsm is large is not the position of the puncture needle 3. Prone to occur. Noise and local reflection sources are usually excluded when extracting candidate lines by Hough transform, but they can be easily distinguished when straight lines, such as bones, are ultrasonic reflection sources. It ’s hard. Therefore, in this case, the ultrasonic diagnostic apparatus U of the second embodiment uses the shallow feature value sa in an auxiliary manner.

  As an auxiliary method of using the shallow feature value sa, for example, the above-described partial differential value dsm is multiplied by the shallow feature value sa or added (subtracted). Further, at this time, the ratio of the influence on the partial differential value dsm can be changed by multiplying the partial differential value dsm and the shallow feature value sa by a predetermined coefficient α. Since the insertion position of the puncture needle 3 is shallower than the position of the bone, a correction that relatively reduces the feature value in the deep portion where the shallow feature value sa becomes small is applied to the partial differential value dsm. The puncture needle 3 is distinguished from the bone. In the ultrasonic diagnostic apparatus U of the present embodiment, the position of the puncture needle 3 is identified using the feature value sc2 = sa × (−dsm) or the feature value sc3 = α × sa-dsm.

  FIG. 14 is a schematic diagram illustrating an example of changes in the shallow feature value sa, the deep feature value sm, the partial differential value dsm, and the feature amounts sc2 and sc3 with respect to the depth direction.

  As shown in FIG. 14 (a), when the bone P is at a position deeper than the position of the puncture needle 3, since the ultrasonic waves can be concentrated and reflected at the position, the reflected wave intensity is increased. As shown in FIG. 14 (b), there is a large difference in the deep feature value sm between the position of the puncture needle 3 and the position of the bone P. In some cases, the maximum of the partial differential value dsm is the value of the puncture needle 3. It may be difficult to distinguish the location. In addition, when the length of the portion that continues in a straight line becomes large, it becomes difficult to determine an appropriate candidate line using the Hough transform.

  At this time, when the feature amounts sc2 and sc3 are calculated as shown in FIG. 14 (c), the weight corresponding to the shallow feature value sa is smaller in the deeper position with respect to the peak value of the equal partial differential value dsm ( Therefore, a difference occurs in the feature amounts sc2 and sc3, and the position of the puncture needle 3 is identified more easily and reliably.

As described above, the ultrasound diagnostic apparatus U according to the second embodiment generates an ultrasound image inside the subject Q based on the ultrasound signal reflected and received inside the subject Q. The diagnosis apparatus U determines the ultrasonic wave incident direction along the subject Q, that is, the distribution of the ultrasonic signal along the depth direction of the subject Q, for each region of the ultrasonic image. A needle position determination unit that acquires a deep feature value sm related to signal intensity in a region deeper than the target region and determines the position of the puncture needle 3 inserted into the subject Q based on the deep feature value sm. Detection map generation unit 162 and puncture needle identification unit 163, and an enhancement processing unit 164 that performs processing for enhancing the needle position range in the ultrasound image.
Therefore, the puncture needle is reflected by the partial differential value dsm that appropriately changes in accordance with the boundary of the shadow area reflecting the decrease in luminance in the shadow area (acoustic shadow) generated by the puncture needle 3 with respect to the incident ultrasonic wave. Since the position of 3 is easily determined, the puncture needle 3 can be detected easily and more accurately without complicating the configuration and processing contents than in the past.

  In addition, the needle position determination unit (the detection map generation unit 162 and the puncture needle identification unit 163) uses the partial differential value dsm, which is a value related to the rate of change in the incident direction of the deep feature value sm, as the predetermined feature value. The position of the puncture needle 3 is determined based on the feature amount. Therefore, the shadow boundary is appropriately extracted based on the partial differential value dsm, and the puncture needle 3 is easily and appropriately detected.

  In addition, the detection map generation unit 162 and the puncture needle identification unit 163 use the product of the partial differential value dsm, which is a value related to the change rate of the deep feature value sm, and the shallow feature value sa as the predetermined feature value sc2, and the feature. The position of the puncture needle 3 is determined based on the quantity sc2. As described above, the shallow portion feature value sa is used as a weighting coefficient as an auxiliary to the deep portion feature value sm, so that the position of the puncture needle 3 can be determined more easily and reliably.

  Alternatively, the detection map generation unit 162 and the puncture needle identification unit 163 multiply the partial differential value dsm, which is a value related to the change rate of the deep feature value sm, and the shallow feature value sa by a predetermined coefficient α (predetermined). As a predetermined feature value sc3, the position of the puncture needle 3 inserted into the subject is determined based on the feature value sc3. Even in this case, the position of the puncture needle 3 based on the deep feature value sm can be determined more easily and reliably by using the shallow feature value sa as well.

The present invention is not limited to the above-described embodiment, and various modifications can be made.
For example, in the above embodiment, the puncture needle 3 is identified by extracting candidate points in units of pixels. However, the puncture needle 3 is used in combination with a process for reducing random noise using a unit larger than the pixel as a minimum unit. May be detected.

  In the above embodiment, a straight line corresponding to the shape of the puncture needle 3 is detected using the Hough transform. However, a straight line may be detected using another method, and a straight line is not assumed. Alternatively, the boundary position where the deep feature value and the shallow feature value change may be determined as the position of the puncture needle 3 as it is or by connecting with a curve or the like. Even if the puncture needle 3 is not a straight line, a region having a shape corresponding to the shape can be detected.

  In the above embodiment, the average value of the brightness in the area shallower than the pixel to be determined (or the statistical value representative of the brightness distribution such as the median value and the mode value) and the maximum brightness value in the deep area are set. Although each was used, it is not restricted to this. The average value can be used for the brightness of deep areas, or the average value of multiple pixels can be used instead of just the maximum value, and an appropriate value can be selected according to the acquisition position of the diagnostic image. It may be. In the above-described embodiment, all the pixels along the ultrasonic incident direction are equally targeted for calculation of the average value and the maximum value within the range of the diagnostic image. However, weighting may be applied. .

  In the above embodiment, the difference between adjacent pixels is simply taken as the partial differential value, but the average value of the forward difference and the backward difference is used, or the average change amount in a plurality of pixels is obtained and used. You may do it.

  In the above embodiment, the partial differential value ds is binarized to obtain candidate points for the position of the puncture needle 3, and straight lines are detected using these candidate points. Candidate points may be determined based on the relationship of partial differential values ds between pixels to be performed or between pixels along the incident direction of ultrasonic waves. Alternatively, the pixel position determined not to correspond to the position of the puncture needle 3 while calculating the partial differential value ds may be excluded at any time without performing the two-stage process.

  If the diagnostic image contains a structure that is clearly unrelated to the shadow from the beginning, detection of the puncture needle 3 is performed after removing the structure range, filtering, or the like. May be performed.

In the second embodiment, when the position of the puncture needle 3 with the deep feature value sm is not easily determined, the shallow feature value sa is supplementarily used. The position of the puncture needle 3 may be determined more reliably by performing the above-described processing using the part feature value sa.
In addition, details such as the specific structure, processing contents, and procedures shown in the above embodiment can be changed as appropriate without departing from the spirit of the present invention.

DESCRIPTION OF SYMBOLS 1 Ultrasonic diagnostic apparatus main body 2 Ultrasonic probe 3 Puncture needle 4 Attachment part 11 Control part 12 Transmission drive part 13 Reception drive part 14 Transmission / reception switching part 15 Image generation part 16 Image processing part 161 Storage part 162 Detection map generation part 163 Puncture needle identification unit 164 Enhancement processing unit 18 Operation input unit 19 Output display unit 21 Transducer array 210 Transducer 22 Cable L Candidate line Q Subject U Ultrasonic diagnostic apparatus

Claims (13)

An ultrasound diagnostic apparatus that generates an ultrasound image inside a subject based on an ultrasound signal reflected and received inside the subject,
For each region defined by one or a plurality of pixels in the ultrasound image, the distribution of the ultrasound signal along the incident direction of the ultrasound incident on the subject is deeper than the region to be determined A needle position determination unit that acquires a depth feature value related to signal intensity in a region, and determines a position of a puncture needle inserted into the subject based on the depth feature value;
A needle emphasis processing unit that performs processing for emphasizing the position of the puncture needle determined in the ultrasound image;
An ultrasonic diagnostic apparatus comprising:   The needle position determination unit determines a position of the puncture needle based on the predetermined feature amount, with a value related to a rate of change of the depth feature value in the incident direction as the predetermined feature amount. The ultrasonic diagnostic apparatus according to claim 1.   The needle position determination unit obtains the deep feature value and a shallow feature value related to signal intensity in a region shallower than the determination target region, and based on the deep feature value and the shallow feature value, The ultrasonic diagnostic apparatus according to claim 1, wherein the position of the puncture needle inserted into the subject is determined.   The needle position determination unit uses a product of a value related to the rate of change of the depth feature value in the incident direction and the shallow feature value as a predetermined feature amount, and based on the predetermined feature amount, The ultrasonic diagnostic apparatus according to claim 3, wherein the position is determined.   The needle position determination unit uses the sum of a value relating to the rate of change of the depth feature value in the incident direction and a value obtained by multiplying the shallow feature value by a predetermined coefficient as the predetermined feature value. The ultrasonic diagnostic apparatus according to claim 3, wherein the position of the puncture needle inserted into the subject is determined based on the method.   The needle position determination unit determines a position of the puncture needle inserted into the subject based on the predetermined feature amount, using a difference between the deep portion feature value and the shallow portion feature value as a predetermined feature amount. The ultrasonic diagnostic apparatus according to claim 3, wherein:   The needle position determination unit determines a position of a puncture needle inserted into the subject based on a value related to a rate of change of the predetermined feature amount in the incident direction. 6. The ultrasonic diagnostic apparatus according to 6. The needle position determination unit acquires, as the shallow portion characteristic value, any one of an average value, a mode value, and a median value corresponding to the signal intensity in each region in a direction shallower than the determination target region. The ultrasonic diagnostic apparatus according to any one of claims 3 to 7, wherein the apparatus is an ultrasonic diagnostic apparatus. The needle position determination unit acquires a maximum value of a value corresponding to a signal intensity in each region deeper than the determination target region as the depth feature value. The ultrasonic diagnostic apparatus according to claim 1.   The needle position determining unit extracts a plurality of the areas where the predetermined feature amount satisfies a predetermined condition as detection candidate areas, and determines the position of the puncture needle based on the detection candidate areas. The ultrasonic diagnostic apparatus as described in any one of Claims 2, 4-7.   The ultrasonic diagnostic apparatus according to claim 10, wherein the plurality of detection candidate regions are set in units of pixels of the ultrasonic image. A transmitter / receiver for transmitting / receiving the ultrasonic signal;
A transmission / reception control unit for controlling a transmission / reception range by the transmission / reception unit;
With
The transmission / reception control unit is configured to acquire the puncture when acquiring an ultrasonic image for determining the position of the puncture needle by the needle position determination unit rather than acquiring an ultrasonic image without determining the position of the puncture needle. The ultrasonic diagnostic apparatus according to any one of claims 1 to 11, wherein a width in which the ultrasonic wave is incident in a width direction perpendicular to a length direction of the needle is narrowed.   The ultrasonic diagnostic apparatus according to claim 1, wherein the determined shape of the puncture needle is a linear shape.