CN113017787B

CN113017787B - Ultrasonic probe and ultrasonic image display device

Info

Publication number: CN113017787B
Application number: CN202011451810.0A
Authority: CN
Inventors: 石黑稔道
Original assignee: Honda Electronics Co Ltd
Current assignee: Honda Electronics Co Ltd
Priority date: 2019-12-25
Filing date: 2020-12-10
Publication date: 2023-11-28
Anticipated expiration: 2040-12-10
Also published as: CN113017787A

Abstract

The invention provides an ultrasonic probe capable of reliably grasping the insertion position and the insertion direction of a puncture needle just after puncture. The ultrasonic probe 3D includes a 1 st linear transducer array 91 and a 2 nd linear transducer array 92 disposed orthogonal thereto. The 1 st linear transducer array 91 transmits ultrasonic waves that are narrowed in the width direction orthogonal to the arrangement direction of the 1 st transducers 91a and are focused at the 1 st focal point F1. A puncture point P1 is provided near the intersection K1 of the 2 nd linear transducer array 92. The intersection K1 transmits ultrasonic waves that are narrowed in the width direction orthogonal to the arrangement direction of the 2 nd transducer 92a and that are focused at the 2 nd focal point F2 at a position farther than the 1 st focal point F1.

Description

Ultrasonic probe and ultrasonic image display device

Technical Field

The present invention relates to an ultrasonic probe having a structure in which a plurality of linear transducer arrays are arranged in an orthogonal manner, and an ultrasonic image display device that simultaneously displays ultrasonic images of 2 orthogonal interfaces by transmitting and receiving ultrasonic waves using the ultrasonic probe.

Background

In medical fields, a puncture of a living tissue (subject) such as a general injection, a nerve block injection, a blood collection, a catheterization, or the like is widely performed. When performing an operation such as nerve block injection or catheterization, if the target site of the subject is not accurately penetrated, the living tissue may be damaged. Against this background, in recent years, an ultrasonic wave guiding technique has been proposed in which the states of a target site and a puncture needle are captured using an ultrasonic probe, and puncture is performed while observing them with an ultrasonic sectional image.

Conventionally, in an apparatus using an ultrasonic wave guiding technique, a conventional ultrasonic probe (so-called single plane probe) is used to capture one cross-sectional image, and the cross-sectional image is displayed to perform puncture. However, in the conventional device, only one of the cross section and the longitudinal section can be confirmed, and the target portion of the subject and the entire appearance of the puncture needle cannot be captured at the same time. Therefore, even when the puncture needle is not accurately pierced, there is a problem in that it is difficult for the operator to notice the situation. Therefore, in order to perform accurate puncture, the puncture needle must be advanced little by little while repeating the fine probe operation, and the operation is complicated.

Accordingly, the present inventors have conventionally proposed an ultrasonic image display device equipped with an ultrasonic probe (so-called biplane probe) capable of simultaneously observing 2 orthogonal cross sections (cross section and longitudinal section) in order to simultaneously capture the entire view of a target site and a puncture needle (for example, refer to patent document 1). Such an ultrasonic probe is also called a T-probe because it is formed by arranging a linear transducer array for a longitudinal section and a linear transducer array for a cross section in a T shape. Each linear transducer array transmits ultrasonic waves focused and focused in the array width direction, respectively. Further, if the ultrasonic probe is used, it is considered that an operator such as a doctor can capture the entire view of the target site and the puncture needle simultaneously by observing the ultrasonic images of 2 orthogonal cross sections.

In view of the need to more easily and reliably puncture a target site, the present inventors have conventionally proposed an ultrasonic probe having a puncture guide fitting as one type of auxiliary instrument (see, for example, patent document 2). In general, a point (puncture point) at which the tip of the puncture needle first passes on the biological tissue is provided in the vicinity of a portion where the arrays intersect with each other. If the puncture guide fitting is used, the puncture needle can be guided at a predetermined angle and pass through the puncture point along the longitudinal section. In an ultrasonic image display device provided with an ultrasonic probe of patent document 2, a frame-shaped guide mark is displayed so as to indicate in advance a depth position at which the tip of a puncture needle is visible in a cross section. Therefore, when a circular image appears in the guide mark, an operator such as a doctor can grasp the tip position of the puncture needle immediately after passing through the puncture point. At this time, the tip of the puncture needle immediately after passing through the puncture point is first captured only by the ultrasonic beam from the linear vibrator array for cross section. When the puncture needle is inserted deeper, the puncture needle can be captured by the two ultrasonic beams from the linear transducer array for cross section and the linear transducer array for longitudinal section.

Prior art literature

Patent literature

Patent document 1 patent No. 5292581

Patent document 2 patent No. 6019369

Disclosure of Invention

The invention aims to solve the technical problems

In the above-described conventional ultrasonic probe, the slice width is narrowed by focusing 2 ultrasonic beams, respectively, so that a clear sectional image is obtained. However, if the slice width of the ultrasonic beam from the linear transducer array for cross section is narrow, the length of the puncture needle captured by the ultrasonic beam becomes short, and only a small point of a circle can be recognized as the puncture needle in the cross-sectional image of the cross section. Therefore, even if it can be confirmed whether the tip of the puncture needle is located at the center of the cross-sectional image (i.e., whether the insertion position of the puncture needle is correct), it cannot be confirmed whether the insertion direction of the puncture needle is correct. Therefore, for example, when puncturing is performed in a free state without a puncture guide fitting, it is difficult to accurately insert the puncture needle in the direction in the longitudinal section.

Means for solving the problems

The present invention has been made in view of the above-described problems, and an object thereof is to provide an ultrasonic probe capable of grasping an insertion position and an insertion direction of a puncture needle immediately after puncture. Another object of the present invention is to provide an ultrasonic image display device capable of displaying a puncture needle immediately after puncture so that an insertion position and an insertion direction can be easily and intuitively understood when the above-described excellent ultrasonic probe is used.

In order to solve the above problems, the gist of the invention according to claim 1 is an ultrasonic probe comprising: a 1 st linear transducer array for acquiring a 1 st cross-sectional image, the 1 st linear transducer array being formed by arranging a plurality of 1 st transducers on a bottom surface of a probe main body; and a 2 nd linear transducer array for acquiring a 2 nd cross-sectional image, the 2 nd linear transducer array being disposed in a manner orthogonal to the 1 st linear transducer array at least one end portion of the 1 st linear transducer array, the 2 nd linear transducer array being formed by arranging a plurality of 2 nd transducers, wherein a puncture point for passing a puncture needle when puncturing a subject is provided in the vicinity of an intersection point located on an extension portion of the end portion of the 1 st linear transducer array, the 1 st linear transducer array transmitting an ultrasonic wave that is narrowed in a width direction orthogonal to an arrangement direction of the 1 st transducers and is focused at a 1 st focal point, at least the intersection point in the 2 nd linear transducer array transmitting an ultrasonic wave that is narrowed in a width direction orthogonal to an arrangement direction of the 2 nd linear transducer array and is focused at a 2 nd focal point located farther than the 1 st focal point, or an ultrasonic wave that is not focused in the width direction.

Therefore, according to the invention of claim 1, since the slice width of the ultrasonic beam from the crossing portion located near the puncture point becomes wider, the length of the puncture needle caught by the ultrasonic beam becomes longer. Therefore, in the cross-sectional image of the 2 nd cross section, the puncture needle can be recognized as a short line segment extending in the insertion direction of the needle. Therefore, not only the insertion position of the puncture needle immediately after the puncture but also the insertion direction can be grasped.

The gist of the invention according to claim 2 is as follows: in claim 1, the 1 st linear transducer array has an acoustic lens in a cross-sectional convex lens shape formed of a material softer than the subject, the 2 nd linear transducer array has an acoustic lens in a cross-sectional convex lens shape formed of a material harder than the subject, and transmits ultrasonic waves that diverge in the width direction without focusing in the width direction orthogonal to the arrangement direction of the 2 nd transducers.

Therefore, according to the invention of claim 2, the ultrasonic beam emitted from the 1 st linear vibrator array is focused at the 1 st focal point by the acoustic lens in the shape of a cross-sectional convex lens formed of a material softer than the subject. In contrast, the ultrasonic beam emitted from the 2 nd linear transducer array is not concentrated in the width direction orthogonal to the arrangement direction of the 2 nd transducers but diverges in the width direction even though passing through an acoustic lens in the shape of a cross-sectional convex lens formed of a material harder than the subject. Therefore, the slice width of the ultrasonic beam from the crossing portion located near the puncture point becomes wider, so that the length of the puncture needle captured by the ultrasonic beam becomes longer.

The gist of the invention according to claim 3 is as follows: in claim 1, the 1 st linear transducer array has an acoustic lens in a cross-sectional convex lens shape formed of a material softer than the subject, the 2 nd linear transducer array has an acoustic lens in a cross-sectional concave lens shape formed of a material softer than the subject, and transmits ultrasonic waves that diverge in the width direction without focusing in the width direction orthogonal to the arrangement direction of the 2 nd transducers.

Therefore, according to the invention of claim 3, the ultrasonic beam emitted from the 1 st linear vibrator array is focused at the 1 st focal point by the acoustic lens in the shape of the cross-sectional pattern lens formed of a material softer than the subject. In contrast, the ultrasonic beam emitted from the 2 nd linear transducer array is not concentrated in the width direction orthogonal to the arrangement direction of the 2 nd transducers but diverges in the width direction even though passing through an acoustic lens in the shape of a cross-sectional concave lens formed of a material softer than the subject. Therefore, the slice width of the ultrasonic beam from the crossing portion located near the puncture point becomes wider, so that the length of the puncture needle captured by the ultrasonic beam becomes longer.

The gist of the invention according to claim 4 is as follows: in claim 1, the 1 st linear transducer array has an acoustic lens in the shape of a cross-sectional convex lens formed of a material softer than the subject, the 2 nd linear transducer array is formed of a material softer than the subject, at least the intersection in the 2 nd linear transducer array has a flat shape without irregularities, and ultrasonic waves that do not gather in a width direction orthogonal to an arrangement direction of the 2 nd transducers but proceed straight or diverge in the width direction are transmitted.

Therefore, according to the invention of claim 4, the ultrasonic beam emitted from the 1 st linear vibrator array is focused at the 1 st focal point by the acoustic lens in the shape of the cross-sectional pattern lens formed of a material softer than the subject. In contrast, even if the ultrasonic beam emitted from at least the intersection in the 2 nd linear transducer array passes through the intersection in a flat shape without irregularities, the ultrasonic beam does not converge in the width direction orthogonal to the arrangement direction of the 2 nd transducer, but proceeds straight or diverges in the width direction. Therefore, the slice width of the ultrasonic beam from the crossing portion located near the puncture point becomes wider, so that the length of the puncture needle captured by the ultrasonic beam becomes longer.

In order to solve the other problem, the gist of the invention according to claim 5 is an ultrasonic image display apparatus for transmitting and receiving ultrasonic waves to and from a subject when a puncture needle is inserted into the subject, the apparatus being capable of simultaneously displaying a 1 st cross-sectional image corresponding to a 1 st cross-section of the subject and a 2 nd interface image corresponding to a 2 nd cross-section orthogonal to the 1 st cross-section on the same screen, the apparatus comprising: the ultrasonic probe of any one of claims 1 to 4, and a vertical line display section that displays a vertical line extending in a vertical direction through a substantially central portion of the 2 nd cross-sectional image.

Therefore, according to the invention of claim 5, when puncturing is performed at the puncture point, the puncture needle is captured by the ultrasonic beam whose slice width is widened, and the captured image of the front end of the puncture needle appears in the vicinity of the vertical line. The tip of the puncture needle at this time appears as an image of a short line segment extending in the insertion direction of the needle. Therefore, it is possible to compare the image with the image of the tip of the puncture needle with reference to a vertical line extending in the vertical direction, so that the insertion position and the insertion direction can be intuitively understood easily. Therefore, the puncture needle can be accurately inserted in this direction in the longitudinal section.

Effects of the invention

As described above, according to the invention described in claims 1 to 4, it is possible to provide an ultrasonic probe capable of grasping the insertion position and the insertion direction of the puncture needle immediately after the puncture.

Further, according to the invention of claim 5, it is possible to provide an ultrasonic image display device capable of displaying a puncture needle immediately after puncture so that the insertion position and the insertion direction can be easily intuitively understood in the case of using the above-described excellent ultrasonic probe.

Drawings

Fig. 1 is a schematic view showing an entire ultrasonic image display device (angiographic apparatus) according to embodiment 1 embodying the present invention.

Fig. 2 is a block diagram showing an electrical configuration of the angiography apparatus according to embodiment 1.

Fig. 3 is a perspective view showing a probe body of the ultrasonic probe according to embodiment 1.

Fig. 4 is a schematic perspective view showing a1 st linear transducer array and a2 nd linear transducer array included in the ultrasonic probe according to embodiment 1.

Fig. 5 (a) is a schematic plan view of the 1 st linear transducer array and the 2 nd linear transducer array included in the ultrasonic probe of embodiment 1, fig. 5 (b) is a sectional view of line A1-A1 in fig. 5 (a), fig. 5 (c) is a sectional view of line A2-A2 in fig. 5 (a), and fig. 5 (d) is a sectional view of line A3-A3 in fig. 5 (a).

Fig. 6 (a) is a schematic view for explaining the traveling direction of the ultrasonic wave in the section of the line A1-A1 in fig. 5 (a), and fig. 6 (b) is a schematic view for explaining the traveling direction of the ultrasonic wave in the section of the line A3-A3 in fig. 5 (a).

Fig. 7 is a schematic diagram for explaining a method of using an ultrasonic probe according to embodiment 1.

Fig. 8 is an explanatory view showing a1 st cross-sectional image and a2 nd cross-sectional image before the insertion of the puncture needle in embodiment 1.

Fig. 9 is an explanatory view showing a1 st cross-sectional image and a2 nd cross-sectional image after insertion of the puncture needle in embodiment 1.

Fig. 10 (a) is a schematic view showing an image of a puncture needle that appears in a frame-shaped guide mark at the time of performing a puncture when an ultrasonic probe of the conventional art is used, and fig. 10 (b) and 10 (c) are schematic views showing an image of a puncture needle that appears in a frame-shaped guide mark at the time of performing a puncture when the ultrasonic probe of embodiment 1 is used.

Fig. 11 (a) is a schematic plan view of the 1 st linear transducer array and the 2 nd linear transducer array included in the ultrasonic probe according to embodiment 2, fig. 11 (B) is a sectional view of line B1-B1 in fig. 11 (a), fig. 11 (c) is a sectional view of line B2-B2 in fig. 11 (a), and fig. 11 (d) is a sectional view of line B3-B3 in fig. 11 (a).

Fig. 12 (a) is a schematic plan view of the 1 st linear transducer array and the 2 nd linear transducer array included in the ultrasonic probe according to embodiment 3, fig. 12 (b) is a sectional view of line C1-C1 in fig. 12 (a), fig. 12 (C) is a sectional view of line C2-C2 in fig. 12 (a), and fig. 12 (d) is a sectional view of line C3-C3 in fig. 12 (a).

Fig. 13 (a) is a schematic view for explaining the traveling direction of the ultrasonic wave in the section of the line C1-C1 in fig. 12 (a), and fig. 13 (b) is a schematic view for explaining the traveling direction of the ultrasonic wave in the section of the line C3-C3 in fig. 12 (a).

Fig. 14 (a) is a schematic plan view of a 1 st linear transducer array and a 2 nd linear transducer array included in an ultrasonic probe according to another embodiment, fig. 14 (b) is a sectional view of line D1-D1 in fig. 15 (a), fig. 14 (c) is a sectional view of line D2-D2 in fig. 14 (a), and fig. 14 (D) is a sectional view of line D3-D3 in fig. 14 (a).

Fig. 15 (a) is a schematic plan view of a 1 st linear transducer array and a 2 nd linear transducer array included in an ultrasonic probe according to another embodiment, fig. 15 (b) is a sectional view of a line E1-E1 in fig. 15 (a), fig. 15 (c) is a sectional view of a line E2-E2 in fig. 15 (a), and fig. 15 (d) is a sectional view of a line E3-E3 in fig. 15 (a).

Fig. 16 (a) is a schematic view for explaining the traveling direction of the ultrasonic wave in the section of the line E1-E1 in fig. 15 (a), and fig. 16 (b) is a schematic view for explaining the traveling direction of the ultrasonic wave in the section of the line E3-E3 in fig. 15 (a).

Detailed Description

[ embodiment 1 ]

An embodiment of embodying the present invention as a blood vessel imaging device as an ultrasonic image display device will be described in detail below with reference to fig. 1 to 9.

Fig. 1 is a schematic diagram showing the entire vascular imaging device 1 according to the present embodiment, and fig. 2 is a block diagram showing the electrical configuration of the vascular imaging device 1.

As shown in fig. 1 and 2, the blood vessel imaging device 1 of the present embodiment includes a device main body 2 and an ultrasonic probe 3 connected to the device main body 2. For example, the vascular imaging device 1 is used when the puncture needle 6 such as a catheter is inserted into the vein 82 in the living tissue 4 (subject). The blood vessel imaging device 1 simultaneously displays a 2 nd cross-sectional image 8 (short axis image) showing a cross section of the vein 82 and a 1 st cross-sectional image 9 (long axis image) showing a longitudinal section of the vein 82 on the same screen 10 (see fig. 8 to 9).

As shown in fig. 1 to 3, the ultrasonic probe 3 includes a signal cable 11, a probe body 12 connected to the distal end of the signal cable 11, a puncture guide fitting 14 (puncture guide mechanism) detachably fixed to the probe body 12, and a probe-side connector 15 provided on the proximal end of the signal cable 11. The device main body 2 is provided with a connector 16, and a probe-side connector 15 of the ultrasonic probe 3 is connected to the connector 16.

As shown in fig. 2, 3, 4, and 5, the ultrasonic probe 3 can be viewed simultaneously with two orthogonal cross sections (a cross section and a longitudinal section), and therefore the ultrasonic probe 3 is called a biplane probe. The transducer mounting surface 20, which is the bottom surface of the probe body 12, is a contact surface with the living tissue 4, and is formed as a transmitting/receiving surface for transmitting and receiving ultrasonic waves. The 1 st linear transducer array 91 and the 2 nd linear transducer array 92 are arranged on the transducer mounting surface 20. The 1 st linear transducer array 91 is a transducer array for acquiring a longitudinal cross-sectional image (1 st cross-sectional image 9), and is configured by arranging a plurality of 1 st transducers 91 a. As shown in fig. 2, the 1 st linear transducer array 91 extends in the long axis direction Y and is located on the center line L0 of the probe body 12 on the transducer mounting surface 20. The 2 nd linear transducer array 92 is a transducer array for acquiring a cross-sectional image (2 nd cross-sectional image 8), and is configured by arranging a plurality of 2 nd transducers 92 a. As shown in fig. 2, the 2 nd linear transducer array 92 extends in the short axis direction X, and is specifically disposed at one end 93 of the 1 st linear transducer array 91 so as to be orthogonal to the 1 st linear transducer array 91. Since the ultrasonic probe 3 is arranged such that the 1 st linear transducer array 91 and the 2 nd linear transducer array 92 form a substantially T shape, the ultrasonic probe 3 is also called a T-shaped probe.

More specifically, the 1 st vibrator 91a in the 1 st linear vibrator array 91 is linearly arranged along the longitudinal direction Y corresponding to the longitudinal section. Further, the plurality of 2 nd transducers 92a in the 2 nd linear transducer array 92 are linearly arranged along the short axis direction X corresponding to the cross section. In the present embodiment, the number of elements of the 2 nd transducer 92a belonging to the 2 nd linear transducer array 92 is 48, for example, and the number of elements of the 1 st transducer 91a belonging to the 1 st linear transducer array 91 is more than 48 (for example, 80), for example. Therefore, the length of the 1 st linear transducer array 9 in the arrangement direction is longer than the length of the 2 nd linear transducer array 92 in the arrangement direction.

In the ultrasonic probe 3 of the present embodiment, the scanning of ultrasonic waves in the 1 st linear transducer array 91 and the 2 nd linear transducer array 92 arranged in a substantially T-shape starts from, for example, the 2 nd transducer 92a at one end of the 2 nd linear transducer array 92 in the short axis direction X. Then, the 2 nd transducer 92a at the other end of the 2 nd linear transducer array 92 in the short axis direction X sequentially scans the elements one by one. Specifically, ultrasonic waves of, for example, 5MHz are sequentially transmitted element by element in the above direction. Next, ultrasonic scanning is sequentially performed from the 1 st transducer 91a at one end of the 1 st linear transducer array 91 toward the 1 st transducer 91a at the other end in the long axis direction Y located at the substantially center of the 2 nd linear transducer array 92 in the short axis direction X.

In the probe body 12, a positioning portion 31 is provided on an extension line (a center line L0 of the probe body 12 on the transducer mounting surface 20) of the 1 st linear transducer array 91 extending in the longitudinal direction Y and on an end edge portion (an end edge portion on the lower side in fig. 2 and on the left side in fig. 3) of the transducer mounting surface 20. The positioning portion 31 is a recess for guiding the tip 71 side of the puncture needle 6 by abutting against the tip when determining the insertion position of the puncture needle 6 into the living tissue 4. The positioning portion 31 is a puncture point P1, and the puncture point P1 is a position at which the puncture needle 6 passes during puncture, and is provided in the vicinity of a crossing portion K1, and the crossing portion K1 is an extension region of an end portion of the 1 st linear transducer array 91 in the 2 nd linear transducer array 92 (see fig. 5 (a) and the like).

On the transducer mounting surface 20 of the probe body 12 with which the living tissue 4 is in contact, ridges 32 (see fig. 3) for avoiding compression of the observation site of the living tissue 4 are provided along the long axis direction Y at both ends in the short axis direction X. By providing the pair of raised strips 32 on the transducer mounting surface 20 of the probe body 12 so as to be separated from each other, the region between the pair of raised strips 32 on the transducer mounting surface 20 side is not excessively pressed. Therefore, the vein 82 located at the observation site can be prevented from being collapsed, and the vein 82 can be reliably pierced.

As shown in fig. 4, 5, and 6, the acoustic lens 29 and the acoustic lens 30 are disposed on the ultrasonic radiation surface sides of the 1 st linear transducer array 91 and the 2 nd linear transducer array 92, respectively, with the acoustic matching layer 90 interposed therebetween. A backing material (not shown) for preventing the ultrasonic waves from propagating backward is disposed on the opposite side of the ultrasonic wave radiation surfaces of the 1 st linear transducer array 91 and the 2 nd linear transducer array 92. The 1 st linear transducer array 91 of the present embodiment has an acoustic lens 29 having a convex lens shape in cross section, and the acoustic lens 29 is curved so that an outer surface in contact with the living tissue 4 swells. The 2 nd linear transducer array 92 of the present embodiment has an acoustic lens 30 having a convex lens shape in cross section, and the acoustic lens 30 is curved with the same curvature as the acoustic lens 29. However, the two acoustic lenses 29 and 30 are made of different materials. That is, the 1 st acoustic lens 29 for the linear transducer array 91 is formed of a synthetic resin material softer than the living tissue 4, whereas the 2 nd acoustic lens 30 for the linear transducer array 92 is formed of a synthetic resin material harder than the living tissue 4. In other words, the acoustic lens 29 for the 1 st linear transducer array 91 is formed of a material having a sound velocity faster than that of the living tissue 4, whereas the acoustic lens 30 for the 2 nd transducer array 92 is formed of a material having a sound velocity slower than that of the living tissue 4. In the case of the present embodiment, specifically, the acoustic lens 29 is formed using silicone resin, and the acoustic lens 30, which is harder than the acoustic lens 29, is formed using polyimide resin. The acoustic lens 29 may be formed using a relatively soft synthetic resin other than the silicone resin. The acoustic lens 30 may be formed using a relatively hard synthetic resin such as an acrylic resin or a polystyrene resin, in addition to the polyimide resin.

Fig. 6 (a) is a schematic diagram for explaining the traveling direction of the ultrasonic wave in the section of the line A1-A1 in fig. 5 (a). Fig. 6b is a schematic diagram for explaining the traveling direction of the ultrasonic wave in the section of the line A3-A3 in fig. 5 (a). In these figures, downward arrows are drawn. These arrows represent the speed of sound for each section, with longer arrows being faster.

In the case of the 1 st linear transducer array 91 having the acoustic lens 29 made of a material having a faster sound velocity than the living tissue 4, the ultrasonic waves traveling through the living tissue 4 by the widthwise end portions of the acoustic lens 29 reach farther at the same time than the ultrasonic waves traveling through the living tissue 4 by the widthwise central portions of the acoustic lens 29 (see fig. 6 (a)). As a result, the ultrasonic wave emitted from the 1 st linear transducer array 91 is narrowed in the width direction of the 1 st transducer 91a in the entire arrangement direction of the 1 st transducer 91a, and is focused at the 1 st focal point F1.

In contrast, in the case of the 2 nd linear transducer array 92 having the acoustic lens 30 made of a material having a slower sound velocity than the living tissue 4, the ultrasonic waves traveling through the living tissue 4 by the widthwise central portion of the acoustic lens 30 reach farther at the same time than the ultrasonic waves traveling through the living tissue 4 by the widthwise end portion of the acoustic lens 30 (see fig. 6 (b)). As a result, the ultrasonic wave emitted from the 2 nd linear transducer array 92 is dispersed in the entire arrangement direction of the 2 nd transducers 92a including the intersection K1 without being concentrated in the width direction of the 2 nd transducers 92 a.

As shown in fig. 1 and 2, the puncture guide fitting 14 includes: a puncture guide 35 having a guide groove 33 for guiding the puncture needle 6; an angle adjustment mechanism 35 capable of adjusting the insertion angle of the puncture needle 6 in multiple stages; and a fixing portion 36 fitted and fixed to a lower side portion of the probe body 12. The puncture guide fitting 14 guides the puncture needle 6 such that the puncture needle 6 is inserted into the living tissue 4 at a predetermined angle along the longitudinal section shown in the 2 nd cross-sectional image 9 in a state where the puncture needle 6 is positioned at the center of the cross-section shown in the 1 st cross-sectional image 8. The puncture guide fitting 14 of the present embodiment is a resin molded part formed using a flexible resin material.

The lower portion of the probe body 12 has a hammerhead-shaped outer shape (substantially T-shaped), in which a 1 st linear transducer array 91 disposed on the front end side protrudes in the lateral direction (refer to fig. 2 and 3). In the puncture guide fitting 14, the fixing portion 36 is formed in a ring shape along the outer shape of the hammer head. An engagement recess (not shown) is formed on the inner peripheral side of the fixing portion 36, and the puncture guide fitting 14 is fixed to the probe body 12 by engagement of the engagement recess with an engagement projection (not shown) formed on the probe body 12.

In the puncture guide fitting 14, an angle adjustment mechanism 35 is provided at one end of the fixing portion 36, and the puncture needle guide 34 is detachably attached to the angle adjustment mechanism 35. The puncture needle guide 34 protrudes at a position spaced upward from the vibrator mounting surface 20. The angle adjustment mechanism 35 is an adjustment mechanism that moves the puncture needle guide 34 in a plurality of stages in the circumferential direction around the positioning portion 31 of the probe body 12, and is fixedly provided at each position. The angle adjustment mechanism 35 is provided with, for example, a 3-stage switching position.

The guide groove 33 of the puncture needle guide 34 is formed so as to exist on the center line L0 of the probe body 12 and extend along the center line L0 when projected from the transducer mounting surface 20. The puncture needle guide 34 is constituted by 2 bar-shaped members 40, and is formed so that the shape as viewed from above is substantially U-shaped, the bar-shaped members 40 extending in a direction parallel to the arrangement direction of the 1 st vibrator 91a in the 1 st linear vibrator array 91 and the base end portions being connected to each other. In the puncture needle guide 34, the gap provided between the 2 rod-like members 40 is a guide groove 33. In a state where the puncture guide fitting 14 is attached to the probe body 12, a guide groove 33 is disposed on the center line L0 of the probe body 12. The guide groove 33 is provided with an opening 41 for introducing the puncture needle 6 and a bottom 42 for abutting the introduced puncture needle 6. The guide groove 33 of the puncture needle guide 34 is provided with a puncture needle introduction portion 43, and the puncture needle introduction portion 43 is formed so that the groove width gradually becomes wider toward the opening 41 side.

The insertion angle of the puncture needle 6 is determined by combining the bottom 42 of the guide groove 33 and the positioning portion 31 of the probe body 12. That is, the insertion angle of the puncture needle 6 into the living tissue 4 is determined by bringing the distal end 71 of the puncture needle 6 into contact with the positioning portion 31 of the probe body 12 and bringing the side surface of the puncture needle 6 into contact with the bottom portion 42 of the guide groove 33. In the puncture guide fitting 14, the insertion angle of the puncture needle 6 defined by the bottom portion 42 and the positioning portion 31 is adjusted in multiple steps by changing the position of the bottom portion 42 of the guide groove 33 by moving the puncture needle guide portion 34 by operating the angle adjustment mechanism 35.

Next, the electrical configuration of the angiography apparatus 1 will be described in detail with reference to fig. 2.

As shown in fig. 2, the apparatus main body 2 of the blood vessel imaging apparatus 1 includes a controller 50, a pulse generating circuit 51, a transmitting circuit 52, a receiving circuit 53, a signal processing section 54, an image processing section 55, a memory 56, a storage device 57, an input device 58, a display device 59, and the like. The controller 50 is a computer including a known Central Processing Unit (CPU), and executes a control program using the memory 56 to control the entire device in a unified manner.

The pulse generating circuit 51 operates in response to a control signal from the controller 50 to generate and output a pulse signal having a prescribed period. The transmission circuit 52 includes a plurality of delay circuits (not shown) corresponding to the number of elements of the respective linear transducer arrays 91, 1 st linear transducer 91 of the linear transducer array 92, and linear transducer 92 in the ultrasonic probe 3. The transmission circuit 52 outputs driving pulses delayed according to the transducers 91a and 92a of the linear transducer arrays 91 and 92 based on the pulse signals output from the pulse generation circuit 51. The delay time for each driving pulse is set so that the ultrasonic wave output from the ultrasonic probe 3 is focused at a predetermined irradiation point.

The receiving circuit 53 includes a signal amplifying circuit, a delay circuit, and a phase modulation adding circuit, which are not shown. In the reception circuit 53, each reflected wave signal (echo signal) received by each of the linear transducer array 91, the transducer 91a of the linear transducer array 92, and the transducer 92a in the ultrasonic probe 3 is amplified. Then, the receiving circuit 53 adds a delay time in consideration of the reception directivity to each reflected wave signal, and then performs a phase modulation addition operation. By this addition, the phase difference of the reception signals of the 1 st transducer 91a and the 2 nd transducer 92a is adjusted.

The signal processing unit 54 is configured by a logarithmic conversion circuit, an envelope detection circuit, an a/D conversion circuit, and the like, which are not shown, and generates data (B-mode data) representing signal intensity in brightness based on the reflected wave signal data from the receiving circuit 53. The logarithmic conversion circuit logarithmic-converts the reflected wave signal, and the envelope detection circuit detects an envelope of the output signal of the logarithmic conversion circuit. Further, the a/D conversion circuit converts the analog signal output from the envelope detection circuit into a digital signal.

The image processing unit 55 performs predetermined image processing based on the B-mode data generated by the signal processing unit 54, and generates a B-mode ultrasound image. Specifically, the image processing unit 55 generates image data having a luminance corresponding to the amplitude (signal strength) of the reflected wave signal. The generated image data is in turn stored in the memory 56. Here, image data of the 2 nd cross-sectional image 8 showing the cross-section of the living tissue 4 and image data of the 1 st cross-sectional image 9 showing the longitudinal section of the living tissue 4 are generated and stored in the memory 56. The 2 nd cross-sectional image 8 and the 1 st cross-sectional image 9 of the living tissue 4 are displayed on the display device 59 in black and white based on the image data of one frame amount stored in the memory 56.

The input device 58 is constituted by a keyboard 61, a trackball 62, and the like, and is used for inputting a request, an instruction, and the like from a user. The display device 59 is, for example, a display such as an LCD or CRT, and displays the 1 st cross-sectional image 9 and the 2 nd cross-sectional image 8 of the living tissue 4 and input screens for various settings.

As shown in fig. 8 to 10, the 1 st cross-sectional image 9 and the 2 nd cross-sectional image 8 are simultaneously displayed side by side on the screen 10 of the display device 59 of the present embodiment. If a virtual straight line L2 extending linearly in the screen vertical direction exists in the center portion of the 2 nd cross-sectional image 8, a 1 st guide line 65 (vertical line) indicating the traveling direction of the puncture needle 6 is actually displayed at a position corresponding to the virtual straight line L2. Further, on the 1 st cross-sectional image 9, a 2 nd guide line 66 indicating the travel path of the puncture needle 6 at the insertion angle is displayed so as to extend straight from the upper left to the lower right of the screen. In the present embodiment, the guide lines 65 and 66 on the 1 st cross-sectional image 8 and the 2 nd cross-sectional image 9 are displayed in the same line type (for example, broken line) and line color (for example, yellow).

A position display section that indicates in advance to the operator the depth position at which the tip of the puncture needle 6 is visible is displayed on the 1 st cross-sectional image 9 and on the 2 nd cross-sectional image 8. In the present embodiment, the horizontal line 67 and the guide mark 68 are displayed as a position display unit. The guide mark 68 of the present embodiment is a frame-like mark that displays a quadrangle of the cross-sectional image in a frame at the intersection position of the guide line 65 and the horizontal line 67 on the 2 nd cross-sectional image 8. The guide mark 68 has a size (for example, a size of about 1.5 times to 3 times) larger than that of a portion corresponding to the diameter of the image corresponding to the distal end 71 of the puncture needle 6. In the present embodiment, the controller 50 serves as a guide mark display unit, and causes the display device 59 to display the guide mark 68.

The horizontal line 67 is a line horizontal to the transducer mounting surface 20 of the probe body 12. The horizontal line 67 is displayed in a different line type (e.g., a dot-dash line) and a different line color (e.g., green) from the guide lines 65, 66. On the other hand, the guide marks 68 are displayed in the same line type (e.g., broken line) and line color (e.g., yellow) as the guide lines 65, 66. The image data of the guide lines 65 and 66, the horizontal line 67, and the guide mark 68 are stored in the memory 56, and the controller 50 reads out the image data and displays the image data on the display device 59.

The storage device 57 is a magnetic disk device, an optical disk device, or the like, and stores a control program and various data in a recording medium. The controller 50 transfers the program or data from the storage device 57 to the memory 56 and sequentially executes the program or data according to the instruction from the input device 58. The program executed by the controller 50 may be a program stored in a storage medium such as a memory card, a Flexible Disk (FD), a CD-ROM, a DVD, or an optical disk, or a program downloaded via a communication medium, and is installed in the storage device 57 for use when executed.

Next, an example of operation when the catheter needle 6 is inserted into the vein 82 of the living tissue 4 using the angiographic apparatus 1 of the present embodiment will be described.

Here, an operator such as a doctor first determines the insertion angle of the puncture needle 6 suitable for the treatment site of the patient. Then, the operator operates the angle adjustment mechanism 35 to set the insertion angle, and attaches the puncture guide fitting 14, in which the position of the puncture needle guide 34 is set, to the probe body 12. Then, the operator operates the keyboard 61 of the input device 58 as the position information input unit to input position information corresponding to the set position of the insertion angle of the puncture needle 6 set by the angle adjustment mechanism 35. At this time, the controller 50 temporarily stores the position information in the memory 56. In the present embodiment, description will be made mainly assuming that the puncture guide fitting 14 is not provided and the puncture operation is performed, in which the operator can perform the puncture without attaching the puncture guide fitting 14 to the probe body 12.

Then, the operator applies an acoustic medium (sterile gel or aseptic gel) to the surface of the living tissue 4 (for example, the surface of the forearm 4a having the vein 82 as shown in fig. 7) serving as the treatment site, and then brings the transducer mounting surface 20 of the probe body 12 into contact with the surface via the acoustic medium. Therefore, when the operator operates a scan start button (not shown) provided on the input device 58, the controller 50 determines the button operation and starts processing for displaying the cross-sectional images 8 and 9 of the living tissue 4.

In this process, the controller 50 causes the pulse generating circuit 51 to operate, and starts transmitting and receiving ultrasonic waves through the ultrasonic probe 3. Specifically, the pulse generating circuit 51 operates in response to a control signal output from the controller 50, and supplies a pulse signal of a prescribed period to the transmitting circuit 52. Then, the transmission circuit 52 generates a driving pulse having a delay time corresponding to the transducers 91a and 92a of the linear transducer arrays 91 and 92 based on the pulse signal, and supplies the driving pulse to the ultrasonic probe 3. Thereby, the transducers 91a and 92a of the linear transducer arrays 91 and 92 of the ultrasonic probe 3 vibrate, and the ultrasonic waves are irradiated to the living tissue 4. A part of the ultrasonic wave propagating through the living tissue 4 is reflected by a tissue boundary surface (for example, a blood vessel wall) or the like of the living tissue 4, and is received by the ultrasonic probe 3. At this time, the reflected wave is converted into an electric signal (reflected wave signal) by the transducers 91a, 92a of the respective linear transducer arrays 91, 92 of the ultrasonic probe 3. The reflected wave signal is amplified in the receiving circuit 53 and then inputted to the signal processing unit 54.

The signal processing unit 54 performs signal processing such as logarithmic conversion, envelope detection, and a/D conversion, and supplies the reflected wave signal converted into a digital signal to the image processing unit 55. The image processing unit 55 performs image processing for generating image data of the cross-sectional images 8 and 9 based on the reflected wave signal. The controller 50 temporarily stores each image data generated by the image processing unit 55 in the memory 56.

The controller 50 reads out the image data stored in the memory 56, and generates display data for causing the display device 59 to display the 1 st cross-sectional image 9 and the 2 nd cross-sectional image 8. The controller 50 as an insertion angle determination unit reads out position information stored in the memory 56, and determines the insertion angle of the puncture needle 6 based on the position information. The controller 50 as a guide wire display unit generates display data of the guide wires 65 and 66 corresponding to the insertion angle of the puncture needle 6. The controller 50 as a position display means predicts a depth position at which the tip 71 of the puncture needle 6 is initially visible in the 1 st cross-sectional image 9 and the 2 nd cross-sectional image 8 based on the insertion angle of the puncture needle 6, and generates display data indicating the depth position to the position display unit (horizontal line 67 and guide mark 68) of the operator in advance.

Then, the controller 50 outputs the generated display data of the cross-sectional image 8, the cross-sectional image 9, the guide line 65, the guide line 66, the horizontal line 67, and the guide mark 68 to the display device 59, respectively. As a result, as shown in fig. 8, the 1 st cross-sectional image 9 and the 2 nd cross-sectional image 8 are simultaneously displayed side by side on the screen 10 of the display device 59. Then, the guide lines 65, 66, the horizontal lines 67, and the guide marks 68 are superimposed on the cross-sectional images 8 and 9 (guide mark display step). In the present embodiment, the cross-sectional image 8 and the cross-sectional image 9 are displayed on the rear side, and the guide line 65, the horizontal line 67, and the guide mark 68 are superimposed on the front side. Further, a guide line 66 and a horizontal line 67 are overlapped on the front side of the 1 st cross-sectional image 9.

Next, the operator visually recognizes the 1 st cross-sectional image 9 and the 2 nd cross-sectional image 8 displayed on the display device 59, and adjusts the position of the ultrasonic probe 3. Specifically, first, a cross section of the vein 82 is photographed on the 2 nd cross-sectional image 8 (short axis image), and the 2 nd linear transducer array 92 side of the ultrasonic probe 3 is moved so that the 1 st guide line 65 on the 2 nd cross-sectional image 8 is located at the center of the vein 82. Then, the 1 st linear transducer array 91 side of the ultrasonic probe 3 is moved so that the direction (axial direction) in which the vein 82 extends coincides with the longitudinal direction Y of the probe body 12, so that the longitudinal section of the vein 82 is imaged along the 1 st cross-sectional image 9 (long axis image). In this case, the 1 st linear transducer array 91 (long axis side) which is the rear side is swung left and right to perform alignment while maintaining the position of the 2 nd linear transducer array 92 (short axis side) of the ultrasonic probe 3.

Here, the operator determines whether or not the insertion angle of the puncture needle 6 is an angle suitable for puncturing the vein 82 based on the horizontal line 67 and the guide mark 68 on the 1 st cross-sectional image 9 and the 2 nd cross-sectional image 8, and the 2 nd guide line 66 on the 2 nd cross-sectional image 8. In addition, fig. 8 shows a 1 st cross-sectional image 9 and a 2 nd cross-sectional image 8 before the insertion of the puncture needle 6. On section 1 image 9 and section 2 image 8, horizontal line 67 and guide mark 68 are located above the treatment site for puncturing vein 82. When it is determined that the insertion angle of the puncture needle 6 is an angle suitable for puncturing the vein 82, the operator brings the distal end 71 of the puncture needle 6 into contact with the position of the positioning portion 31 of the probe body 12 from the oblique direction, and inserts the puncture needle 6 into the living tissue 4 (forearm 4 a) in this state.

Fig. 9 shows the 1 st section image 9 and the 2 nd section image 8 after insertion of the puncture needle 6. Thus, the puncture needle 6 is displayed on the 1 st cross-sectional image 9 and the 2 nd cross-sectional image 8. Here, first, the puncture needle 6 is displayed within the frame of the guide mark 68 of the 2 nd cross-sectional image 8, and then is displayed on the 2 nd guide line 66 of the 2 nd cross-sectional image 9. That is, the tip of the puncture needle 6 immediately after passing through the puncture point P1 is first captured by the ultrasonic beam from the 2 nd linear transducer array 92 for the 2 nd cross-sectional image. When the puncture needle 6 is inserted deeper, it is captured by the ultrasonic beams from the 1 st linear vibrator array 91 and the 2 nd linear vibrator array 92.

Fig. 10 (a) is a schematic diagram showing an image of a puncture needle appearing in a frame-shaped guide mark 68 at the time of performing puncture when an ultrasonic probe of the conventional art is used. In the case of the ultrasonic probe of the conventional art, as in the 1 st linear transducer array 91, the ultrasonic wave also narrows in the width direction of the 2 nd linear transducer array 92, and is focused at the 1 st focal point F1. Therefore, the slice width of the ultrasonic beam from the intersection K1 located near the puncture point P1 becomes narrow. Therefore, the length of the puncture needle 6 captured by the ultrasonic beam becomes short, and the puncture needle 6 is displayed as a small dot in a circle within the guide mark 68 of the 2 nd cross-sectional image 8 (short axis image). In this case, the operator cannot grasp whether the insertion direction of the puncture needle 6 is correct.

On the other hand, fig. 10 (b) and 10 (c) are schematic views showing images of the puncture needle 6 appearing in the frame-shaped guide mark 68 at the time of puncture when the ultrasonic probe 3 of the present embodiment is used. In the case of the present embodiment, the slice width of the ultrasonic beam from the intersection K1 located near the puncture point P1 becomes wider. As a result, the length of the puncture needle 6 captured by the ultrasonic beam becomes longer. Thus, within the guide mark 68 of the 2 nd cross-sectional image 8 (short axis image), the puncture needle 6 is displayed as a short line segment extending in the insertion direction of the needle. Therefore, not only the insertion position of the puncture needle 6 immediately after the puncture but also the insertion direction can be grasped. In fig. 10 (b), the stub section is shown extending in the up-down direction of the 2 nd cross-sectional image 8. Therefore, since it can be grasped that the puncture needle 6 is inserted in the correct direction, the operator only needs to push the puncture needle 6 in the same direction directly. In contrast, in fig. 10 (c), the displayed stub section extends in a direction slightly inclined from the up-down direction of the 2 nd cross-sectional image 8. Therefore, since it can be grasped that the puncture needle 6 is not inserted in the correct direction, the operator needs to review the insertion direction again. That is, the insertion direction is corrected so as to be a line extending in the direction of fig. 10 (b), and then the puncture needle 6 may be advanced.

And, when the operator judges that the front end 71 of the puncture needle 6 has reached the blood vessel wall of the vein 82 in the above-described manner, the operator immediately penetrates the blood vessel wall with the front end 71 of the puncture needle 6 and inserts the front end 71 of the puncture needle 6 into the vein 82. After confirming that the front end 71 of the puncture needle 6 has reached the inside of the vein 82 based on the 2 nd cross-sectional image 8, the operator stops the puncturing operation of the puncture needle 6.

When the operator operates a scan end button (not shown) provided on the input device 58, the controller 50 determines that the button has been operated, and ends the process for displaying the cross-sectional images 8 and 9 of the living tissue 4. Then, the operator moves the probe body 12 along the guide groove 33 while maintaining the puncture state (retaining the puncture path) of the puncture needle 6. The operator removes the ultrasonic probe 3 from the puncture needle 6 through the opening 41 of the guide groove 33. The operator then manipulates the catheter, inserts the catheter into vein 82, and performs prescribed treatment.

Thus, according to the present embodiment, the following effects can be obtained.

(1) In the ultrasonic probe 3 of the present embodiment, the 1 st linear transducer array 91 has an acoustic lens 29, and the acoustic lens 29 has a convex lens shape in cross section and is formed of a material softer than the living tissue 4. On the other hand, the 2 nd linear transducer array 92 has an acoustic lens 30, and the acoustic lens 30 is formed of a harder material than the living tissue 4 in a convex lens shape in a cross section. Accordingly, the ultrasonic beam emitted from the 1 st linear transducer array 91 is focused at the 1 st focal point F1 by the above-described acoustic lens 29. In contrast, the ultrasonic beam emitted from the 2 nd linear transducer array 92 is not focused but diverged even by the acoustic lens 30. Therefore, the slice width of the ultrasonic beam from the crossing portion K1 located near the puncture point P1 becomes wider, so that the length of the puncture needle 6 captured by the ultrasonic beam becomes longer. Thus, in the 2 nd cross-sectional image 8, the puncture needle 6 can be recognized as a short line segment extending in the needle insertion direction. Therefore, not only the insertion position of the puncture needle 6 immediately after the puncture but also the insertion direction can be grasped. In addition, since the acoustic lens 29 and the acoustic lens 30 are each in the shape of a cross-sectional convex lens, the ultrasonic probe 3 is less likely to get stuck when moving along the skin or the like, and the movement is smooth. Therefore, the advantage of the use feeling is the same as the conventional one.

(2) The blood vessel imaging device 1 of the present embodiment includes the ultrasonic probe 3 and a vertical line display unit that displays a vertical line (1 st guide line 65) extending in the vertical direction through the substantially central portion of the 2 nd cross-sectional image 8. Therefore, when puncturing is performed at the puncture point P1, the puncture needle 6 is captured by the ultrasonic beam whose slice width is widened, and the captured image of the front end of the puncture needle 6 appears in the vicinity of the 1 st guide line 65. The tip of the puncture needle 6 at this time is represented as an image of a short line segment extending in the insertion direction of the needle. Therefore, the insertion position and the insertion direction can be intuitively understood by comparing the position of the 1 st guide wire 65 with the image of the distal end of the puncture needle 6. Therefore, the puncture needle 6 can be accurately inserted in this direction in the longitudinal section. The blood vessel imaging device 1 further includes a guide mark display unit that displays a frame-shaped guide mark 68 on the 2 nd cross-sectional image 8, and the frame-shaped guide mark 68 indicates in advance a depth position at which the tip of the puncture needle 6 is visible. In the case of the device 1, since the guide mark 68 is displayed on the 2 nd cross-sectional image 8, the position at which the tip of the puncture needle 6 is visible before the puncture is performed can be easily and accurately predicted by visually checking the guide mark 68. When the puncture point P1 is punctured, the puncture needle 6 is captured by the ultrasonic beam having a widened slice width, and the captured image of the tip of the puncture needle 6 appears in the guide mark 68. The tip of the puncture needle 6 at this time is represented as an image of a short line segment extending in the insertion direction of the needle. Therefore, the puncture needle 6 immediately after the puncture can be displayed on the screen in such a manner that the insertion position and the insertion direction can be intuitively understood easily. Therefore, the puncture needle 6 can be accurately inserted in this direction in the longitudinal section. In addition, when puncturing is performed in a free state without the puncture guide fitting, the puncture needle can be inserted accurately and easily in this direction in the longitudinal section.

[ embodiment 2 ]

Next, an ultrasonic probe 3A according to embodiment 2 will be described. Fig. 11 (a) is a schematic plan view of the 1 st linear transducer array 91 and the 2 nd linear transducer array 92 included in the ultrasonic probe 3A, fig. 11 (B) is a sectional view of a line B1-B1 in fig. 11 (a), fig. 11 (c) is a sectional view of a line B2-B2 in fig. 11 (a), and fig. 11 (d) is a sectional view of a line B3-B3 in fig. 11 (a). Here, the differences from the ultrasonic probe 3 of embodiment 1 will be described in detail, and common points are omitted.

In the ultrasonic probe 3 of embodiment 1, the hardness of the materials used in the acoustic lens 29 of the 1 st linear transducer array 91 and the acoustic lens 30 of the 2 nd linear transducer array 92 are different. In contrast, in the ultrasonic probe 3A of the present embodiment, the materials used for the acoustic lens 29 and the acoustic lens 30A are the same synthetic resin material (specifically, silicone resin softer than the living tissue 4), and the hardness is also equal. In contrast, in the ultrasonic probe 3A, the acoustic lens 29 on the 1 st linear transducer array 91 side has a convex lens shape in cross section, whereas the acoustic lens 30A on the 2 nd linear transducer array 92 side has a concave lens shape in cross section.

In the present embodiment, with this configuration, as a result, the ultrasonic beam emitted from the 1 st linear transducer array 91 is focused at the 1 st focal point F1 by the above-described cross-section convex lens-shaped acoustic lens 29. In contrast, the ultrasonic beam emitted from the 2 nd linear transducer array 92 is not condensed but diverged even by the above-described cross-section concave lens-shaped acoustic lens 30A. Therefore, the slice width of the ultrasonic beam from the crossing portion K1 located near the puncture point P1 becomes wider, so that the length of the puncture needle 6 captured by the ultrasonic beam becomes longer. Accordingly, as shown in fig. 10 (b) and 10 (c), in the 2 nd cross-sectional image 8, the puncture needle 6 can be recognized as a short line segment extending in the needle insertion direction. Therefore, not only the insertion position of the puncture needle 6 immediately after the puncture but also the insertion direction can be grasped. The ultrasonic probe 3A has an advantage that only one material is required for the acoustic lens 29 and the acoustic lens 30A. Therefore, for example, 2 acoustic lenses 29 and 30A may be manufactured separately or may be manufactured integrally.

[ embodiment 3 ]

Next, an ultrasonic probe 3B according to embodiment 3 will be described. Fig. 12 (a) is a schematic plan view of the 1 st linear transducer array 91 and the 2 nd linear transducer array 92 included in the ultrasonic probe 3B, fig. 12 (B) is a sectional view of a line C1-C1 in fig. 12 (a), fig. 12 (C) is a sectional view of a line C2-C2 in fig. 12 (a), and fig. 12 (d) is a sectional view of a line C3-C3 in fig. 12 (a). Here, the differences from the ultrasonic probe 3 of embodiment 1 will be described in detail, and common points are omitted.

In the ultrasonic probe 3 of embodiment 1 described above, the 1 st linear transducer array 91 is covered with the acoustic lens 29 having a convex lens shape in cross section in the entire arrangement direction of the 1 st transducer 91 a. This point is the same as the 1 st linear transducer array 91 of the present embodiment. In the ultrasonic probe 3 according to embodiment 1, the 2 nd linear transducer array 92 is covered with the acoustic lens 30 having a convex lens shape in cross section in the entire arrangement direction of the 2 nd transducers 92 a. In contrast, the 2 nd linear transducer array 92 of the present embodiment is partially covered with the acoustic lens 30B having a convex lens shape in cross section, not with respect to the entire arrangement direction of the 2 nd transducers 92 a. That is, the acoustic lens 30B of the present embodiment is divided into two parts in a state where the intermediate part (i.e., the crossing part K1) is exposed. Therefore, the intersection K1 where the acoustic lens 30B is not present is formed as the flat portion 94 having a flat shape with no surface irregularities.

Fig. 13 (a) is a schematic view for explaining the traveling direction of the ultrasonic wave in the section of the line C1-C1 in fig. 12 (a). As shown in the figure, the ultrasonic wave emitted from the 1 st linear transducer array 91 is narrowed in the width direction of the 1 st transducer 91a in the entire arrangement direction of the 1 st transducer 91a, and is concentrated at the 1 st focal point F1. The same applies to the ultrasonic waves emitted from the portion other than the crossing portion K1 of the 2 nd linear transducer array 92. Fig. 13 (b) is a schematic view for explaining the traveling direction of the ultrasonic wave in the section of line C3-C3 in fig. 12 (a). As shown in the figure, the ultrasonic wave emitted from the intersection K1 of the 2 nd linear transducer array 92 linearly advances without being concentrated in the width direction of the 2 nd transducer 92 a. Therefore, the slice width of the ultrasonic beam from the crossing portion K1 located near the puncture point P1 becomes wider, so that the length of the puncture needle 6 captured by the ultrasonic beam becomes longer. Accordingly, as shown in fig. 10 (a) and 10 (c), in the 2 nd cross-sectional image 8, the puncture needle 6 can be recognized as a short line segment extending in the needle insertion direction. Therefore, not only the insertion position of the puncture needle 6 immediately after the puncture but also the insertion direction can be grasped. The ultrasonic probe 3B has an advantage that only one material is required for the acoustic lens 29 and the acoustic lens 30B. Therefore, for example, 2 acoustic lenses 29 and 30B may be manufactured separately or may be manufactured integrally.

The embodiment of the present invention may be modified as follows.

In embodiment 3, the 2 nd linear transducer array 92 is exposed only at the middle portion (i.e., the crossing portion K1) in the arrangement direction of the 2 nd transducers 92a, and the other portions are covered with the acoustic lens 30B having a convex lens shape in cross section. In contrast, the ultrasonic probe 3C of the other embodiments shown in fig. 14 (a) to (d) may be used. That is, in the present embodiment, the acoustic lens is not present at all in the 2 nd linear transducer array 92, and the acoustic matching layer 90 is entirely exposed. Therefore, the entire region of the 2 nd linear transducer array 92 including the intersection K1 is formed as a flat portion 94 having a flat shape with no surface irregularities. That is, the acoustic lens having a convex lens shape in cross section to cover the 2 nd linear transducer array 92 may be omitted partially or entirely. According to this configuration, the acoustic lens is provided with a smaller area than in embodiment 1 and the like, and therefore, there is an advantage of low cost.

In embodiment 3, the 2 nd linear transducer array 92 omits the acoustic lens 30B having a convex lens shape in cross section at the middle portion (i.e., the crossing portion K1) in the arrangement direction of the 2 nd transducers 92 a. In contrast, for example, the acoustic lens 30 having a convex lens shape in cross section may be provided over the entire area, and various kinds of processing may be performed so that only the intersecting portion K1 is formed in a flat shape without irregularities. For example, the flat portion 94 may be formed by flattening the synthetic resin at the crossing portion K1 by grinding, dissolving, or the like, or the flat portion 94 may be formed by further coating, adhering, or the like, the synthetic resin at the crossing portion K1.

For example, another embodiment of the ultrasonic probe 3D shown in fig. 15 (a) to 15 (D) may be used. In this ultrasonic probe 3D, the materials used for the acoustic lens 29 and the acoustic lens 30C are the same synthetic resin material (specifically, silicone resin softer than the living tissue 4), and the hardness is also equal. The acoustic lens 29 on the 1 st linear transducer array 91 side and the acoustic lens 30C on the 2 nd linear transducer array 92 side are each formed in a cross-sectional convex lens shape. However, the curvature of the acoustic lens 30C shown in fig. 15 (C) and 15 (d) is set to a value smaller than the curvature of the acoustic lens 29 shown in fig. 15 (b). Accordingly, as shown in fig. 16 (a), the ultrasonic wave emitted from the 1 st linear transducer array 91 is narrowed in the width direction of the 1 st transducer 91a in the entire arrangement direction of the 1 st transducer 91a, and is concentrated at the 1 st focal point F1. As shown in fig. 16b, the ultrasonic wave emitted from the 2 nd linear transducer array 92 is narrowed in the width direction of the 2 nd transducer 92a in the entire arrangement direction of the 2 nd transducer 92a, and is concentrated at the 2 nd focal point F2 at a position farther than the 1 st focal point F1. Therefore, the slice width of the ultrasonic beam from the crossing portion K1 located near the puncture point P1 becomes wider, so that the length of the puncture needle 6 captured by the ultrasonic beam becomes longer.

In embodiment 1, the acoustic matching layer 90 is disposed between the 1 st linear transducer array 91 and the 2 nd linear transducer array 92 and the acoustic lenses 29 and 30, but the acoustic matching layer 90 is not necessarily required and may be omitted.

In the blood vessel imaging device 1 according to embodiment 1, a selection function for setting the horizontal line 67 and the guide mark 68 to be displayed or not may be provided. Specifically, the controller 50 may display a selection button for setting the horizontal line 67 and the guide mark 68 to be displayed or not displayed on the setting screen of the display device 59. And, the controller 50 displays or eliminates the horizontal line 67 and the guide mark 68 on the 1 st cross-sectional image 9 and the 2 nd cross-sectional image 8 based on the button operation of the operator. For example, a skilled operator who is used to the operation of the blood vessel photographing device 1 can predict the position where the front end 71 of the puncture needle 6 is visible from the positions of the guide lines 65 and 66 displayed in the sectional images 8 and 9. Therefore, when the vascular photographing device 1 is used by a skilled operator, the puncture of the puncture needle 6 can be performed without displaying the horizontal line 67 and the guide mark 68. Further, when the blood vessel imaging device 1 is used by an operator who is not familiar with the operation, the puncture needle 6 can be reliably and safely pierced by displaying the horizontal line 67 and the guide mark 68.

In embodiment 1, the guide mark 68 as the position display unit has a square frame shape, but may have a triangular or circular frame shape. The guide mark 68 is not limited to a frame-shaped mark, and may be, for example, a cross-shaped mark, a dot-shaped mark, or the like, as long as the position can be recognized. Alternatively, the guide mark 68 may not be displayed.

In the blood vessel imaging device 1 of each of the above embodiments, the catheter treatment is performed by displaying the cross-sectional image 8 and the cross-sectional image 9 of the vein 82 or the like, but the blood vessel imaging device 1 may be used in the case of performing other operations such as blood collection. The present invention is not limited to the blood vessel imaging device 1, and may be embodied as an ultrasonic image display device that displays a cross-sectional image of a nerve or the like in addition to a blood vessel, and performs other operations such as nerve block injection.

Description of the reference numerals

Vascular photographing device as ultrasonic image display device

3. 3A, 3B, 3C, 3D

Biological tissue as a subject

6. puncture needle

Image of section 2

Image of section 1

Probe body

Vibrator installation surface as bottom surface

29. 30, 30A, 30B, 30C

Controller as guide mark display section, vertical line display section

65. the 1 st guide line as vertical line

68. guide marks

71. front end of puncture needle

91. vibrator 1

1 st linear vibrator array

93. (end of the 1 st linear vibrator array)

92a. 2 nd vibrator

92. the 2 nd linear vibrator array

F1. focus 1

F2. focus 2

K1. crossing points

P1. puncture site.

Claims

1. An ultrasonic probe, comprising: a 1 st linear transducer array for acquiring a 1 st cross-sectional image, the 1 st linear transducer array being formed by arranging a plurality of 1 st transducers on a bottom surface of a probe main body; and a 2 nd linear transducer array for acquiring a 2 nd cross-sectional image, the 2 nd linear transducer array being formed by arranging a plurality of 2 nd transducers in at least one end portion of the 1 st linear transducer array so as to be orthogonal to the 1 st linear transducer array, wherein a puncture point for passing a puncture needle when puncturing a subject is provided in the vicinity of an intersection portion located on an extension portion of the end portion of the 1 st linear transducer array in the 2 nd linear transducer array,

The 1 st linear transducer array transmits ultrasonic waves which are narrowed in a width direction orthogonal to an arrangement direction of the 1 st transducers and are concentrated at a 1 st focus,

at least the intersection in the 2 nd linear transducer array transmits ultrasonic waves that are narrowed in a width direction orthogonal to the arrangement direction of the 2 nd transducers and that are focused at a 2 nd focal point located farther than the 1 st focal point, or ultrasonic waves that are not focused in the width direction.

2. The ultrasonic probe of claim 1, wherein the probe comprises a probe body,

the 1 st linear transducer array has an acoustic lens in the shape of a cross-sectional convex lens formed of a material softer than the subject,

the 2 nd linear transducer array has an acoustic lens in the shape of a cross-sectional convex lens formed of a material harder than the subject, and transmits ultrasonic waves that are not concentrated in a width direction orthogonal to an arrangement direction of the 2 nd transducers but diverge in the width direction.

3. The ultrasonic probe of claim 1, wherein the probe comprises a probe body,

the 2 nd linear transducer array has an acoustic lens in the shape of a cross-section concave lens formed of a material softer than the subject, and transmits ultrasonic waves that are not concentrated in a width direction orthogonal to an arrangement direction of the 2 nd transducers but diverge in the width direction.

4. The ultrasonic probe of claim 1, wherein the probe comprises a probe body,

the 2 nd linear vibrator array is formed of a softer material than the subject,

at least the intersection in the 2 nd linear transducer array has a flat shape without irregularities, and transmits ultrasonic waves that are not concentrated in a width direction orthogonal to an arrangement direction of the 2 nd transducers but are dispersed in the width direction.

5. An ultrasonic image display device capable of simultaneously displaying a 1 st cross-sectional image corresponding to a 1 st cross-section of a subject and a 2 nd interface image corresponding to a 2 nd cross-section orthogonal to the 1 st cross-section on the same screen by transmitting and receiving ultrasonic waves to the subject when a puncture needle is inserted into the subject, comprising:

the ultrasonic probe of any one of claims 1-4, and

and a vertical line display unit that displays a vertical line extending in a vertical direction through a substantially central portion of the 2 nd cross-sectional image.