CN113017787A

CN113017787A - Ultrasonic probe and ultrasonic image display device

Info

Publication number: CN113017787A
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: 2021-06-25
Anticipated expiration: 2040-12-10
Also published as: CN113017787B

Abstract

The invention provides an ultrasonic probe which can reliably grasp the insertion position and the insertion direction of a puncture needle immediately after puncture. The ultrasonic probe 3D includes a1 st linear transducer array 91 and a2 nd linear transducer array 92 arranged orthogonal to the 1 st linear transducer array 91. The 1 st linear transducer array 91 transmits ultrasonic waves narrowed in the width direction orthogonal to the arrangement direction of the 1 st transducers 91a and focused at the 1 st focal point F1. A puncture point P1 is provided in the vicinity of the intersection K1 of the 2 nd linear transducer array 92. The intersection K1 transmits an ultrasonic wave narrowed in the width direction orthogonal to the arrangement direction of the 2 nd transducer 92a and condensed at the 2 nd focal point F2 located 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 orthogonally, 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 practice, actions of puncturing a living tissue (subject) such as general injection, nerve block injection, blood collection, catheterization, and the like are widely performed. When a nerve block injection or a catheter insertion operation is performed, if a target site of a subject is not accurately punctured, a living tissue may be damaged. Under such a background, in recent years, an ultrasonic guidance technique has been proposed in which the states of a target site and a puncture needle are captured using an ultrasonic probe, and the puncture is performed while observing them with an ultrasonic sectional image.

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

Therefore, in order to capture the entire view of the target region and the puncture needle at the same time, the inventors of the present application have proposed an ultrasonic image display device equipped with an ultrasonic probe (so-called double-plane probe) that can be observed simultaneously with 2 orthogonal cross sections (a cross section and a longitudinal section) (see, for example, patent document 1). Such an ultrasonic probe is also called a T-type probe because it is formed by arranging a linear transducer array for a longitudinal section and a linear transducer array for a transverse section in a T-shape. Each of the linear transducer arrays transmits ultrasonic waves focused and focused in the array width direction, respectively. Further, if this ultrasonic probe is used, it is considered that the operator such as a doctor can simultaneously capture the entire appearance of the target site and the puncture needle by observing the ultrasonic images of the orthogonal 2 cross sections.

In view of the need to more easily and reliably puncture a target site, the inventors of the present application have previously proposed an ultrasonic probe having a puncture guide fitting as one type of an auxiliary instrument (see, for example, patent document 2). In general, a point (puncture point) through which the tip of the puncture needle passes first in the living tissue is provided in the vicinity of a portion where arrays intersect with each other. Further, 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 the ultrasonic probe of patent document 2, a frame-shaped guide mark is displayed in order to indicate a depth position at which the tip of the puncture needle starts to be visible in a cross section in advance. Therefore, when the circular image appears in the guide mark, the operator such as a doctor can grasp the position of the tip 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 line transducer array for the cross section. When the puncture needle is inserted deeper, the two ultrasonic beams from the linear transducer array for the cross section and the linear transducer array for the longitudinal section can be captured.

Documents of the prior art

Patent document

Patent document 1 patent No. 5292581 publication

Patent document 2 patent No. 6019369

Disclosure of Invention

Technical problem to be solved by the invention

In the above-described conventional ultrasonic probe, the slice width is narrowed by condensing 2 ultrasonic beams respectively, thereby obtaining a clear sectional image. However, if the slice width of the ultrasonic beam from the line transducer array for cross section is narrow, the length of the puncture needle captured by the ultrasonic beam becomes short, and the puncture needle can be recognized only as a small circular spot in the cross-sectional image of the cross section. Therefore, even if it can be confirmed whether the tip of the puncture needle is positioned at the center of the cross-sectional image (i.e., whether the insertion position of the puncture needle is correct), it is not possible to confirm 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 this direction in a vertical cross section.

Means for solving the problems

The present invention has been made in view of the above 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 ultrasound image display apparatus capable of displaying a puncture needle immediately after puncture so that an insertion position and an insertion direction can be easily intuitively understood when the above excellent ultrasound probe is used.

In order to solve the above problems, the gist of the invention according to claim 1 is an ultrasonic probe including: a1 st linear transducer array for acquiring a1 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 body; and a2 nd linear transducer array for acquiring a2 nd cross-sectional image, the 2 nd linear transducer array being formed by arranging a plurality of 2 nd transducers, the 2 nd linear transducer array being arranged such that at least one end portion of the 1 st linear transducer array is orthogonal to the 1 st linear transducer array, wherein a puncture point for passing a puncture needle when a subject is punctured 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, the 1 st linear transducer array transmitting an ultrasonic wave which is narrowed in a width direction orthogonal to an arrangement direction of the 1 st transducers and focused at a1 st focal point, and at least the intersection portion of the 2 nd linear transducer array transmitting an ultrasonic wave which is focused at a2 nd focal point which is narrowed in a width direction orthogonal to an arrangement direction of the 2 nd linear transducer array and is positioned farther than the 1 st focal point, Or ultrasonic waves that do not converge in the width direction.

Therefore, according to the invention according to claim 1, the slice width of the ultrasonic beam from the intersection portion located in the vicinity of the puncture point is increased, so that the length of the puncture needle captured by the ultrasonic beam is increased. 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 described in claim 2 is as follows: in claim 1, the 1 st line oscillator array has an acoustic lens having a convex lens shape in cross section formed of a material softer than the subject, and the 2 nd line oscillator array has an acoustic lens having a convex lens shape in cross section formed of a material harder than the subject, and transmits an ultrasonic wave which is not condensed in a width direction orthogonal to an arrangement direction of the 2 nd oscillators and is diverged in the width direction.

Therefore, according to the invention of claim 2, the ultrasonic beam emitted from the 1 st linear transducer array is condensed at the 1 st focal point by the acoustic lens having a cross-sectional convex lens shape formed of a material softer than the subject. In contrast, the ultrasonic beam emitted from the 2 nd linear transducer array does not converge in the width direction orthogonal to the arrangement direction of the 2 nd transducers but diverges in the width direction even by the acoustic lens having a convex lens shape in cross section formed of a material harder than the subject. Therefore, the slice width of the ultrasonic beam from the intersection portion located in the vicinity of the puncture point becomes wide, and the length of the puncture needle captured by the ultrasonic beam becomes long.

The gist of the invention described in claim 3 is as follows: in claim 1, the 1 st line vibrator array has an acoustic lens having a convex lens shape in cross section formed of a material softer than the subject, and the 2 nd line vibrator array has an acoustic lens having a concave lens shape in cross section formed of a material softer than the subject, and transmits an ultrasonic wave which is not condensed in a width direction orthogonal to an arrangement direction of the 2 nd vibrators but is diverged in the width direction.

Therefore, according to the invention recited in claim 3, the ultrasonic beam emitted from the 1 st line oscillator array is condensed at the 1 st focal point by the acoustic lens in the shape of a 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 does not converge in the width direction orthogonal to the arrangement direction of the 2 nd transducers but diverges in the width direction even by the acoustic lens having a concave lens shape in cross section formed of a material softer than the subject. Therefore, the slice width of the ultrasonic beam from the intersection portion located in the vicinity of the puncture point becomes wide, and the length of the puncture needle captured by the ultrasonic beam becomes long.

The gist of the invention described in claim 4 is as follows: in claim 1, the 1 st line oscillator array has an acoustic lens having a convex lens shape in cross section formed of a material softer than the subject, the 2 nd line oscillator array is formed of a material softer than the subject, at least the intersection portion in the 2 nd line oscillator array has a flat shape without unevenness, and transmits an ultrasonic wave which does not converge in a width direction orthogonal to the arrangement direction of the 2 nd elements but linearly advances or diverges in the width direction.

Therefore, according to the invention described in claim 4, the ultrasonic beam emitted from the 1 st line oscillator array is condensed at the 1 st focal point by the acoustic lens in the shape of a cross-sectional pattern lens formed of a material softer than the subject. In contrast, the ultrasonic beam emitted from at least the intersection portion in the 2 nd linear transducer array does not converge in the width direction orthogonal to the arrangement direction of the 2 nd transducers but linearly advances or diverges in the width direction even if it passes through the intersection portion having a flat shape without irregularities. Therefore, the slice width of the ultrasonic beam from the intersection portion located in the vicinity of the puncture point becomes wide, and the length of the puncture needle captured by the ultrasonic beam becomes long.

In order to solve the above another problem, the gist of the invention according to claim 5 is an ultrasonic image display device that can simultaneously display a1 st cross-sectional image corresponding to a1 st cross-section of a subject and a2 nd interface image corresponding to a2 nd cross-section orthogonal to the 1 st cross-section on the same screen by transmitting and receiving ultrasonic waves to and from the subject when a puncture needle is inserted into the subject, the ultrasonic image display device including: the ultrasonic probe according to 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 sectional image.

Therefore, according to the invention of claim 5, when the puncture 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 tip 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 extending in the needle insertion direction. Therefore, the image of the puncture needle tip can be compared with the image of the puncture needle tip with reference to a vertical line extending in the vertical direction, and the insertion position and the insertion direction can be intuitively understood. Therefore, the puncture needle can be accurately inserted in the longitudinal section in this direction.

Effects of the invention

As described above, according to the inventions 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 described in claim 5, it is possible 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 intuitively understood in the case of using the excellent ultrasonic probe.

Drawings

Fig. 1 is an overall schematic view showing an ultrasonic image display device (blood vessel imaging device) according to embodiment 1 of the present invention.

Fig. 2 is a block diagram showing an electrical configuration of the blood vessel imaging 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 and 2 nd linear transducer arrays included in the ultrasonic probe according to embodiment 1, fig. 5(b) is a cross-sectional view taken along line a1-a1 in fig. 5(a), fig. 5(c) is a cross-sectional view taken along line a2-a2 in fig. 5(a), and fig. 5(d) is a cross-sectional view taken along 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 cross 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 cross 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 in embodiment 1.

Fig. 8 is an explanatory view showing the 1 st and 2 nd cross-sectional images before the puncture needle is inserted in embodiment 1.

Fig. 9 is an explanatory view showing the 1 st cross-sectional image and the 2 nd cross-sectional image after the puncture needle is inserted in embodiment 1.

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

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

Fig. 12(a) is a schematic plan view of the 1 st and 2 nd linear transducer arrays included in the ultrasonic probe according to embodiment 3, fig. 12(b) is a cross-sectional view taken along line C1-C1 in fig. 12(a), fig. 12(C) is a cross-sectional view taken along line C2-C2 in fig. 12(a), and fig. 12(d) is a cross-sectional view taken along 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 cross section of line C1-C1 in fig. 12(a), and fig. 6(b) is a schematic view for explaining the traveling direction of the ultrasonic wave in the cross section of line C3-C3 in fig. 12 (a).

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

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

Detailed Description

[ embodiment 1 ]

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

Fig. 1 is a schematic diagram showing the entire blood vessel imaging apparatus 1 according to the present embodiment, and fig. 2 is a block diagram showing an electrical configuration of the blood vessel imaging apparatus 1.

As shown in fig. 1 and 2, a blood vessel imaging apparatus 1 of the present embodiment includes an apparatus body 2 and an ultrasonic probe 3 connected to the apparatus body 2. The blood vessel imaging apparatus 1 is used, for example, when a puncture needle 6 such as a catheter is inserted into a vein 82 in a living tissue 4 (subject). The blood vessel imaging apparatus 1 simultaneously displays a2 nd sectional image 8 (short axis image) showing a cross section of the vein 82 and a1 st sectional image 9 (long axis image) showing a vertical 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 accessory 14 (puncture guide mechanism) detachably fixed to the probe body 12, and a probe-side connector 15 provided at 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 simultaneously observed in two orthogonal cross sections (a transverse section and a longitudinal section), and thus the ultrasonic probe 3 is called a double-plane type 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 transmission/reception surface for transmitting and receiving ultrasonic waves. On the transducer mounting surface 20, a1 st linear transducer array 91 and a2 nd linear transducer array 92 are arranged. The 1 st linear transducer array 91 is a transducer array for obtaining a vertical sectional image (1 st sectional image 9), and is arranged by arranging a plurality of 1 st transducers 91a. As shown in fig. 2, the 1 st linear transducer array 91 extends in the longitudinal direction Y and is positioned 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 sectional image 8), and is configured by arranging a plurality of 2 nd transducers 92a. As shown in fig. 2, the 2 nd linear transducer array 92 extends in the minor axis direction X, and specifically is 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 and 2 nd

linear transducer arrays

91 and 92 form a substantially T-shape, the ultrasonic probe 3 is also referred to as a T-type probe.

More specifically, the 1 st elements 91a in the 1 st linear element array 91 are linearly arranged along the long axis direction Y corresponding to the longitudinal section. Further, the plurality of 2 nd elements 92a in the 2 nd linear element 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 vibrator 92a belonging to the 2 nd linear vibrator array 92 is, for example, 48, and the number of elements of the 1 st vibrator 91a belonging to the 1 st linear vibrator array 91 is, for example, a number (for example, 80) larger than 48. Therefore, the length of the 1 st linear transducer array 9 in the array direction is longer than the length of the 2 nd linear transducer array 92 in the array direction.

In the ultrasonic probe 3 of the present embodiment, the scanning of the ultrasonic waves in the 1 st and 2 nd

linear transducer arrays

91 and 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 minor axis direction X. Then, the 2 nd transducer 92a at the other end of the 2 nd linear transducer array 92 in the minor axis direction X is sequentially subjected to ultrasonic scanning element by element. Specifically, ultrasonic waves of, for example, 5MHz are sequentially transmitted element by element in the above-described direction. Next, ultrasonic scanning is sequentially performed element by element from the 1 st transducer 91a at one end of the 1 st linear transducer array 91 to the 1 st transducer 91a at the other end in the long axis direction Y located at the approximate center of the 2 nd linear transducer array 92 in the short axis direction X.

In the probe body 12, the positioning portion 31 is provided on an extended line of the 1 st linear transducer array 91 extending in the longitudinal direction Y (the center line L0 of the probe body 12 on the transducer mounting surface 20) and an end edge portion (the lower side in fig. 2 and the left end edge portion in fig. 3) of the transducer mounting surface 20. The positioning portion 31 is a concave portion for guiding the puncture needle 6 by abutting the distal end 71 side of the puncture needle 6 when the insertion position of the puncture needle 6 into the living tissue 4 is determined. The positioning unit 31 is a puncture point P1, the puncture point P1 is a position through which the puncture needle 6 passes during puncture, and is provided in the vicinity of an intersection K1, and the intersection K1 is an extension region of the end 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, convex portions 32 (see fig. 3) for avoiding pressure on the observation site of the living tissue 4 are provided along the major axis direction Y at both ends in the minor axis direction X. By providing the pair of ridges 32 on the transducer mounting surface 20 of the probe body 12 so as to be spaced apart from each other, the region between the pair of ridges 32 on the transducer mounting surface 20 side is not pressed too strongly. Therefore, the vein 82 located at the observation site can be prevented from being crushed, and the vein 82 can be reliably punctured.

As shown in fig. 4, 5, and 6, the acoustic lens 29 and the acoustic lens 30 are disposed on the ultrasonic wave emitting surface side of the 1 st and 2 nd

linear transducer arrays

91 and 92, respectively, with the acoustic matching layer 90 interposed therebetween. Further, a backing material (not shown) for preventing backward propagation of ultrasonic waves is disposed on the opposite side of the ultrasonic wave radiation surface of the 1 st and 2 nd

linear transducer arrays

91 and 92. The 1 st linear transducer array 91 of the present embodiment includes the acoustic lens 29 having a convex lens shape in cross section, and the acoustic lens 29 is curved so that the outer surface in contact with the living tissue 4 is expanded. The 2 nd linear transducer array 92 of the present embodiment includes the acoustic lens 30 having a convex lens shape in cross section, and the acoustic lens 30 is curved with the same curvature as that of the acoustic lens 29. However, the two

acoustic lenses

29 and 30 are made of different materials. That is, the acoustic lens 29 for the 1 st linear transducer array 91 is formed using a synthetic resin material softer than the living tissue 4, whereas the acoustic lens 30 for the 2 nd linear transducer array 92 is formed using 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 using a material having a higher sound velocity than the biological tissue 4, whereas the acoustic lens 30 for the 2 nd transducer array 92 is formed using a material having a lower sound velocity than the biological tissue 4. In the case of the present embodiment, specifically, the acoustic lens 29 is formed using silicone resin, and the acoustic lens 30 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 above-described 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 view for explaining the traveling direction of the ultrasonic wave in the cross section of line a1-a1 in fig. 5 (a). Fig. 6b is a schematic view for explaining the traveling direction of the ultrasonic wave in the cross section of line A3-A3 in fig. 5 (a). In these figures a downward arrow is drawn. These arrows represent the speed of sound for each section, the longer the arrows, the faster the speed of sound.

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 wave traveling through the living tissue 4 via the end portions in the width direction of the acoustic lens 29 reaches farther in the same time than the ultrasonic wave traveling through the living tissue 4 via the center portion in the width direction 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 over the entire arrangement direction of the 1 st transducers 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 wave traveling through the width-direction central portion of the acoustic lens 30 in the living tissue 4 arrives farther than the ultrasonic wave traveling through the living tissue 4 through the width-direction end portions of the acoustic lens 30 in the same time (see fig. 6 (b)). As a result, the ultrasonic waves emitted from the 2 nd linear transducer array 92 are not condensed and are dispersed in the width direction of the 2 nd transducer 92a in the entire arrangement direction of the 2 nd transducer 92a including the intersection K1.

As shown in fig. 1 and 2, the puncture guide fitting 14 includes: a puncture guide 35 in which a guide groove 33 for guiding the puncture needle 6 is formed; an angle adjusting mechanism 35 capable of adjusting the insertion angle of the puncture needle 6 in multiple stages; and a fixing portion 36 fitted into and fixed to a lower portion of the side surface of the probe body 12. The puncture guide metal fitting 14 guides the puncture needle 6 so that the puncture needle 6 is inserted into the living tissue 4 at a predetermined angle along the vertical cross section shown in the 2 nd cross-sectional image 9 in a state where the puncture needle 6 is positioned at the center portion 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 the 1 st linear transducer array 91 disposed on the tip side projects in the lateral direction (see 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. For example, an engaging concave portion (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 the engaging concave portion engaging with an engaging convex portion (not shown) formed on the probe body 12.

In the puncture guide metal fitting 14, an angle adjusting mechanism 35 is provided at one end of the fixing portion 36, and a puncture needle guide portion 34 is detachably attached to the angle adjusting mechanism 35. The puncture needle guide unit 34 protrudes at a position separated upward from the transducer mounting surface 20. The angle adjustment mechanism 35 is an adjustment mechanism that moves the puncture needle guide portion 34 in multiple 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, 3-stage switching positions.

The guide groove 33 of the puncture needle guide portion 34 is formed so as to be present 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 unit 34 is formed of 2 rod members 40, and is formed in a substantially U-shape when viewed from the top, and the rod members 40 are extended in a direction parallel to the arrangement direction of the 1 st transducer 91a in the 1 st linear transducer array 91, and have base end portions connected to each other. In the puncture needle guide 34, the gaps provided between the 2 rod members 40 are guide grooves 33. In a state where the puncture guide fitting 14 is attached to the probe body 12, the 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 against which the introduced puncture needle 6 abuts. Further, a puncture needle introduction portion 43 is provided in the guide groove 33 of the puncture needle guide portion 34, and the puncture needle introduction portion 43 is formed such that the groove width gradually increases toward the opening 41 side.

Also, the insertion angle of the puncture needle 6 is determined by combining the bottom portion 42 of the guide groove 33 and the positioning portion 31 of the probe main body 12. That is, the insertion angle of the puncture needle 6 into the living tissue 4 is determined by bringing the tip 71 of the puncture needle 6 into contact with the positioning portion 31 of the probe main body 12 and bringing the side surface of the puncture needle 6 into contact with the bottom 42 of the guide groove 33. In the puncture guide fitting 14, the insertion angle of the puncture needle 6 determined by the bottom 42 and the positioning portion 31 is adjusted in multiple stages by operating the angle adjustment mechanism 35 to move the puncture needle guide portion 34 and change the position of the bottom 42 of the guide groove 33.

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

As shown in fig. 2, the apparatus 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 unit 54, an image processing unit 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 a memory 56 to collectively control the entire apparatus.

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 each of the linear transducer arrays 91 in the ultrasonic probe 3, the 1 st linear transducer 91 in the linear transducer array 92, and the linear transducers 92. The transmission circuit 52 outputs a drive pulse delayed by the

transducers

91a and 92a of the linear transducer array 91 and the linear transducer array 92 based on the pulse signal output from the pulse generation circuit 51. The delay time of 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 tone adding circuit, which are not shown. In the receiving 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 reception circuit 53 adds a delay time considering reception directivity to each reflected wave signal, and then performs phase adjustment and addition. By this addition, the phase difference of the reception signals of the 1 st oscillator 91a and the 2 nd oscillator 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 (not shown), and generates data (B-mode data) representing the signal intensity at the brightness level based on the reflected wave signal data from the receiving circuit 53. A logarithmic conversion circuit logarithmically converts the reflected wave signal, and an envelope detection circuit detects an envelope of an output signal of the logarithmic conversion circuit. 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 to generate a B-mode ultrasonic image. Specifically, the image processing unit 55 generates image data having a luminance corresponding to the amplitude (signal intensity) of the reflected wave signal. The generated image data are sequentially stored in the memory 56. Here, image data of the 2 nd sectional image 8 showing the cross section of the living tissue 4 and image data of the 1 st sectional image 9 showing the vertical section of the living tissue 4 are generated and stored in the memory 56. Then, based on the image data for one frame 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.

The input device 58 is composed of 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 a display such as an LCD or a CRT, and displays the 1 st and 2

nd sectional images

9 and 8 of the living tissue 4 and an input screen 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 in parallel on the left and right sides on the screen 10 of the display device 59 according to the present embodiment. Assuming that a virtual straight line L2 extending linearly in the vertical direction of the screen exists in the center of the 2 nd cross-sectional image 8, the 1 st guide line 65 (vertical line) indicating the advancing 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, a2 nd guide line 66 indicating the traveling 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 sectional image 8 and the 2 nd sectional image 9 are displayed in the same line shape (for example, a broken line) and line color (for example, yellow).

Then, a position display section which indicates a depth position at which the tip of the puncture needle 6 starts to be visible to the operator in advance is displayed on the 1 st cross-sectional image 9 and on the 2 nd cross-sectional image 8. In the present embodiment, a horizontal line 67 and a guide mark 68 are displayed as a position display unit. The guide mark 68 of the present embodiment is a quadrangular frame-like mark that displays the cross-sectional image within a frame at the intersection 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 to 3 times) larger than a size 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 functions as a guide mark display unit and causes the display device 59 to display a 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 mark 68 is 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 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 in accordance with an 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 when executed, the program is installed in the storage device 57 and used.

Next, an example of an operation when the puncture needle 6 of the catheter is inserted into the vein 82 of the living tissue 4 using the blood vessel imaging device 1 according to the present embodiment will be described.

Here, the 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 so as 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 the 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. The operator can perform the puncture without attaching the puncture guide accessory 14 to the probe body 12, and in the present embodiment, the description will be given mainly assuming that the puncture operation is performed without the puncture guide accessory 14.

Then, the operator applies an acoustic medium (a sterile gel or a sterile gel) to the surface of the living tissue 4 to be a treatment site (for example, the surface of the forearm 4a having the vein 82 as shown in fig. 7), and then brings the transducer mounting surface 20 of the probe body 12 into contact with 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 operation of the button and starts the process for displaying the

cross-sectional images

8 and 9 of the living tissue 4.

In this process, the controller 50 operates the pulse generation circuit 51 to start transmission and reception of ultrasonic waves by the ultrasonic probe 3. Specifically, the pulse generation 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 transmission circuit 52. Then, the transmission circuit 52 generates a drive 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 drive 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 irradiate the living tissue 4 with ultrasonic waves. A part of the ultrasonic waves propagating through the living tissue 4 are reflected by a tissue boundary surface (for example, a blood vessel wall) of the living tissue 4, and received by the ultrasonic probe 3. At this time, the reflected waves are converted into electrical signals (reflected wave signals) by the

transducers

91a and 92a of the

linear transducer arrays

91 and 92 of the ultrasonic probe 3. The reflected wave signal is amplified in the receiving circuit 53, and the like, and then input 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

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 each 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 the 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, which is a guide line display unit, generates display data of the guide lines 65 and 66 corresponding to the insertion angle of the puncture needle 6. Further, the controller 50 as the position display means predicts a depth position at which the tip 71 of the puncture needle 6 starts to be visible in the 1 st sectional image 9 and the 2 nd sectional image 8 based on the insertion angle of the puncture needle 6, and generates display data of a position display section (the horizontal line 67 and the guide mark 68) that indicates the depth position to the operator in advance.

Then, the controller 50 outputs the generated display data of the

cross-sectional images

8 and 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 in parallel on the left and right sides on the screen 10 of the display device 59. Then, the guide line 65, the guide line 66, the horizontal line 67, and the guide mark 68 are superimposed and displayed on the cross-sectional images 8 and 9 (guide mark display step). In the present embodiment, the

sectional images

8 and 9 are displayed on the back side, and the guide line 65, the horizontal line 67, and the guide mark 68 are superimposed on the front side. Further, the guide line 66 and the horizontal line 67 are superimposed on the near side of the 1 st sectional image 9.

Next, the operator visually recognizes the 1 st and 2

nd sectional images

9 and 8 displayed on the display device 59, and adjusts the position of the ultrasonic probe 3. Specifically, first, the cross section of the vein 82 is taken 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 positioned at the center of the vein 82. Then, the 1 st line 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 axis direction Y of the probe body 12, so as to take a vertical section of the vein 82 along the 1 st sectional image 9 (long axis image). At this time, the position of the ultrasonic probe 3 on the 2 nd linear transducer array 92 side (short axis side) is maintained, and the 1 st linear transducer array 91 side (long axis side) which is the rear side is swung left and right to perform positioning.

Here, the operator determines whether 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 the 1 st and 2 nd

cross-sectional images

9 and 8 before the puncture needle 6 is inserted. On the 1 st and 2

nd sectional images

9 and 8, the horizontal line 67 and the guide mark 68 are located above the treatment site for puncturing the vein 82. When determining that the insertion angle of the puncture needle 6 is an angle suitable for puncturing the vein 82, the operator inserts the puncture needle 6 into the living tissue 4 (forearm 4a) in a state in which the tip 71 of the puncture needle 6 is brought into contact with the position of the positioning portion 31 of the probe body 12 from an oblique direction.

Fig. 9 shows the 1 st and 2

nd sectional images

9, 8 after insertion of the puncture needle 6. Therefore, the puncture needle 6 is displayed on the 1 st cross-sectional image 9 and the 2 nd cross-sectional image 8. Here, the puncture needle 6 is first displayed within the frame of the guide mark 68 of the 2 nd cross-sectional image 8, and then 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 only 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 further, it is captured by the ultrasonic beams from the 1 st and 2 nd

linear transducer arrays

91 and 92.

Fig. 10(a) is a schematic diagram showing an image of the puncture needle appearing in the frame-shaped guide mark 68 when the puncture is performed when the ultrasonic probe of the conventional technique is used. In the case of the ultrasonic probe of the conventional technique, as in the case of the 1 st linear transducer array 91, the ultrasonic wave is narrowed in the width direction of the 2 nd transducer 92a also in 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 in the vicinity of 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 circular dot 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 diagrams showing images of the puncture needle 6 appearing in the frame-shaped guide mark 68 at the time of performing puncture when the ultrasound 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 in the vicinity of the puncture point P1 is increased. As a result, the length of the puncture needle 6 captured by the ultrasonic beam becomes longer. Therefore, 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 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 fig. 10(b), a short line segment is shown extending in the up-down direction of the 2 nd 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 directly push the puncture needle 6 in the same direction. In contrast, in fig. 10(c), the short line segment shown extends in a direction slightly inclined from the up-down direction of the 2 nd 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 puncture needle 6 may be pushed after the insertion direction is corrected so as to be a line segment extending in the direction of fig. 10 (b).

When the operator judges that the tip 71 of the puncture needle 6 has reached the blood vessel wall of the vein 82 in the above-described manner, the operator subsequently penetrates the blood vessel wall with the tip 71 of the puncture needle 6 and inserts the tip 71 of the puncture needle 6 into the vein 82. After confirming that the distal 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 puncture 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 keeping the puncture state (puncture path remaining) of the puncture needle 6. Then, the operator removes the ultrasound probe 3 from the puncture needle 6 through the opening 41 of the guide groove 33. Then, the operator operates the catheter, inserts the catheter into the vein 82, and performs a predetermined treatment.

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

(1) In the ultrasound probe 3 of the present embodiment, the 1 st linear transducer array 91 includes the acoustic lens 29, and the acoustic lens 29 has a cross-sectional convex lens shape and is formed of a material softer than the living tissue 4. On the other hand, the 2 nd linear transducer array 92 has the acoustic lens 30, and the acoustic lens 30 is formed of a material harder than the living tissue 4, in a convex lens shape in cross section. Therefore, the ultrasonic beam emitted from the 1 st linear transducer array 91 is condensed 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 condensed but is diverged even by the acoustic lens 30. Therefore, the slice width of the ultrasonic beam from the intersection K1 located in the vicinity of the puncture point P1 becomes wide, and the length of the puncture needle 6 captured by the ultrasonic beam becomes long. Therefore, 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 a sectional convex lens shape, the ultrasonic probe 3 is less likely to be jammed when moving along the skin or the like, and the movement is smooth. Therefore, the use feeling is the same as that of the conventional one.

(2) The blood vessel imaging apparatus 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 a substantially central portion of the 2 nd cross-sectional image 8. Therefore, when the puncture is performed at the puncture point P1, the puncture needle 6 is captured by the ultrasonic beam whose slice width is widened, and an image of the captured tip of the puncture needle 6 appears in the vicinity of the 1 st guide wire 65. The tip of the puncture needle 6 at this time appears as an image of a short line extending in the needle insertion direction. Therefore, the 1 st guide wire 65 position reference can be compared with the image of the distal end of the puncture needle 6, and the insertion position and the insertion direction can be intuitively understood. Therefore, the puncture needle 6 can be accurately inserted in this direction in the longitudinal section. The blood vessel imaging apparatus 1 further includes a guide mark display unit that displays a frame-shaped guide mark 68 on the 2 nd cross-sectional image 8, the frame-shaped guide mark 68 indicating a depth position at which the tip of the puncture needle 6 starts to be visible in advance. In the case of this apparatus 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 becomes visible before the puncture is performed can be easily and accurately predicted by visually checking this guide mark 68. When the puncture point P1 punctures, the ultrasound beam with the increased slice width captures the puncture needle 6, 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 appears as an image of a short line extending in the needle insertion direction. Therefore, the puncture needle 6 immediately after the puncture can be displayed on the screen so that the insertion position and the insertion direction can be intuitively and easily understood. 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 a puncture guide fitting, the puncture needle can be accurately and easily inserted in this direction in a longitudinal section.

[ 2 nd embodiment ]

Next, the ultrasonic probe 3A according to embodiment 2 will be described. Fig. 11(a) is a schematic plan view of the 1 st and 2 nd

linear transducer arrays

91 and 92 included in the ultrasonic probe 3A, fig. 11(B) is a cross-sectional view taken along line B1-B1 in fig. 11(a), fig. 11(c) is a cross-sectional view taken along line B2-B2 in fig. 11(a), and fig. 11(d) is a cross-sectional view taken along line B3-B3 in fig. 11 (a). Here, differences from the ultrasonic probe 3 of embodiment 1 will be described in detail, and common points will be omitted.

In the ultrasonic probe 3 according to embodiment 1 described above, the acoustic lens 29 included in the 1 st line transducer array 91 and the acoustic lens 30 included in the 2 nd line transducer array 92 are made of materials having different hardness. On the contrary, 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, and 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 line transducer array 91 is condensed at the 1 st focal point F1 by the above-described acoustic lens 29 of the sectional convex lens shape. In contrast, the ultrasonic beam emitted from the 2 nd linear transducer array 92 is not condensed but is diverged even by the above-described concave-lens-shaped acoustic lens 30A. Therefore, the slice width of the ultrasonic beam from the intersection K1 located in the vicinity of the puncture point P1 becomes wide, and the length of the puncture needle 6 captured by the ultrasonic beam becomes long. Therefore, 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 kind of 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 integrally.

[ embodiment 3 ]

Next, the ultrasonic probe 3B according to embodiment 3 will be described. Fig. 12(a) is a schematic plan view of the 1 st and 2 nd

linear transducer arrays

91 and 92 included in the ultrasonic probe 3B, fig. 12(B) is a cross-sectional view taken along line C1-C1 in fig. 12(a), fig. 12(C) is a cross-sectional view taken along line C2-C2 in fig. 12(a), and fig. 12(d) is a cross-sectional view taken along line C3-C3 in fig. 12 (a). Here, differences from the ultrasonic probe 3 of embodiment 1 will be described in detail, and common points will be omitted.

In the ultrasound 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 over the entire arrangement direction of the 1 st transducers 91a. This point is the same as the 1 st linear transducer array 91 of the present embodiment. In the ultrasound 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 over the entire arrangement direction of the 2 nd transducers 92a. In contrast, the 2 nd linear transducer array 92 of the present embodiment is partially covered by the acoustic lens 30B having a convex lens shape in cross section, not the entire arrangement direction of the 2 nd transducers 92a. That is, the acoustic lens 30B of the present embodiment is divided into two parts with the intermediate part (i.e., the intersection K1) exposed. Therefore, the intersection K1 where the acoustic lens 30B does not exist is formed as the flat portion 94 having a flat shape without unevenness on the surface.

Fig. 13(a) is a schematic view for explaining the traveling direction of the ultrasonic wave in the cross section of line C1-C1 in fig. 12 (a). As shown in the figure, the ultrasonic waves emitted from the 1 st linear transducer array 91 are narrowed in the width direction of the 1 st transducer 91a over the 1 st transducer 91a in the arrangement direction, and are focused at the 1 st focal point F1. The same applies to ultrasonic waves emitted from a portion other than the intersection K1 in 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 cross section of line C3-C3 in fig. 12 (a). As shown in the figure, the ultrasonic waves emitted from the intersection K1 of the 2 nd linear transducer array 92 travel straight without being focused in the width direction of the 2 nd transducer 92a. Therefore, the slice width of the ultrasonic beam from the intersection K1 located in the vicinity of the puncture point P1 becomes wide, and the length of the puncture needle 6 captured by the ultrasonic beam becomes long. Therefore, 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 kind of 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 integrally.

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

In embodiment 3 described above, the 2 nd linear transducer array 92 is exposed only at the middle portion (i.e., the intersection 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. Conversely, for example, the ultrasonic probe 3C of another embodiment shown in fig. 14(a) to (d) may be used. That is, in the present embodiment, no acoustic lens is present at all in the 2 nd linear transducer array 92, and the entire acoustic matching layer 90 is 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 without unevenness on the surface. That is, the acoustic lens having a convex cross-sectional shape to cover the 2 nd linear transducer array 92 may be omitted only in part or entirely. With this arrangement, the area for providing the acoustic lens is smaller than that of embodiment 1 and the like, and therefore, there is an advantage of cost reduction.

In embodiment 3 described above, the 2 nd linear transducer array 92 omits the acoustic lens 30B having a convex cross-sectional shape at the middle portion (i.e., the intersection K1) in the arrangement direction of the 2 nd transducers 92a. Conversely, 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 intersection K1 is formed into a flat shape without unevenness. For example, the flat portion 94 may be formed by polishing, dissolving, or the like, the synthetic resin of the intersection K1 being flat, or the flat portion 94 may be formed by further applying, adhering, or the like, synthetic resin to the intersection K1.

For example, the ultrasonic probe 3D according to another embodiment shown in fig. 15(a) to 15(D) may be used. In the 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 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). Therefore, 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 transducers 91a, and is focused at the 1 st focal point F1. As shown in fig. 16b, the ultrasonic waves emitted from the 2 nd linear transducer array 92 are narrowed in the width direction of the 2 nd transducer 92a in the entire arrangement direction of the 2 nd transducers 92a, and are focused at the 2 nd focal point F2 located farther than the 1 st focal point F1. Therefore, the slice width of the ultrasonic beam from the intersection K1 located in the vicinity of the puncture point P1 becomes wide, and the length of the puncture needle 6 captured by the ultrasonic beam becomes long.

In embodiment 1 described above, the acoustic matching layer 90 is disposed between the 1 st and 2 nd

linear transducer arrays

91 and 92 and the

acoustic lens

29 and 30, but the acoustic matching layer 90 is not essential and may be omitted.

In the blood vessel imaging apparatus 1 according to embodiment 1 described above, a selection function of setting display or non-display may be provided for the horizontal line 67 and the guide mark 68. 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. Also, the controller 50 displays or eliminates the horizontal line 67 and the guide mark 68 on the 1 st and 2 nd

cross-sectional images

9 and 8 based on the button operation of the operator. For example, a skilled operator who is accustomed to the operation of the blood vessel photographing device 1 can predict the position at which the tip 71 of the puncture needle 6 starts to be visible, based on the positions of the guide lines 65 and 66 displayed in the

sectional images

8 and 9. Therefore, when a skilled operator uses the blood vessel imaging apparatus 1, the puncture needle 6 can be punctured without displaying the horizontal line 67 and the guide mark 68. In addition, when the operator who is not familiar with the operation of the blood vessel imaging apparatus 1 uses the blood vessel imaging apparatus, the horizontal line 67 and the guide mark 68 are displayed, so that the puncture of the puncture needle 6 can be performed securely and reliably.

In embodiment 1, the guide mark 68 as the position display unit has a quadrangular 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 or a dot-shaped mark as long as it is a mark that allows position recognition. Alternatively, the guide mark 68 may not be displayed.

In the blood vessel imaging apparatus 1 according to each of the above embodiments, the catheter treatment is performed by displaying the sectional image 8 and the sectional image 9 of the vein 82 or the like, but the blood vessel imaging apparatus 1 may be used when performing other operations such as blood collection. Further, the present invention is not limited to the blood vessel photographing 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

A blood vessel photographing device as an ultrasonic image display device

3. 3A, 3B, 3C, 3d

A biological tissue as a subject

Puncture needle

2 nd sectional image

1 st sectional image

A probe body

A vibrator mounting surface as a bottom surface

29. 30, 30A, 30B, 30c

A controller as a guide mark display part or a vertical line display part

65.. 1 st guideline as a vertical line

68.

71.. front end of puncture needle

1 st oscillator

91a

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

No. 2 oscillator

92.. 2 nd linear vibrator array

F1

F2.. focal point 2

K1.. intersection site

P1.

Claims

1. An ultrasonic probe, comprising: a1 st linear transducer array for acquiring a1 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 body; and a2 nd linear transducer array for acquiring a2 nd cross-sectional image, the 2 nd linear transducer array being disposed at least at one end portion of the 1 st linear transducer array so as to be orthogonal to the 1 st linear transducer array, and 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 2 nd linear transducer array in the vicinity of an intersection portion located on an extension portion of the end portion of the 1 st linear transducer array,

the 1 st linear transducer array transmits ultrasonic waves that are narrowed in a width direction orthogonal to the array direction of the 1 st transducers and focused at a1 st focal point,

at least the intersection portion of the 2 nd linear transducer array transmits an ultrasonic wave which is narrowed in a width direction orthogonal to the arrangement direction of the 2 nd transducers and focused at a2 nd focal point located farther than the 1 st focal point, or an ultrasonic wave which is not focused in the width direction.

2. The ultrasonic probe of claim 1,

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

the 2 nd linear transducer array has an acoustic lens having a convex lens shape in cross section formed of a material harder than the subject, and transmits an ultrasonic wave which is not condensed in a width direction orthogonal to an arrangement direction of the 2 nd transducers but is diffused in the width direction.

3. The ultrasonic probe of claim 1,

the 2 nd linear transducer array has an acoustic lens having a concave lens shape in cross section formed of a material softer than the subject, and transmits an ultrasonic wave which is not condensed in a width direction orthogonal to an arrangement direction of the 2 nd transducers but is diffused in the width direction.

4. The ultrasonic probe of claim 1,

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

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

5. An ultrasound image display apparatus that can simultaneously display a1 st cross-sectional image corresponding to a1 st cross-section of a subject and a2 nd interface image corresponding to a2 nd cross-section orthogonal to the 1 st cross-section on the same screen by transmitting and receiving ultrasound to and from the subject when a puncture needle is inserted into the subject, the ultrasound image display apparatus 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.