JP4782407B2 - Ultrasonic irradiation device - Google Patents

Ultrasonic irradiation device Download PDF

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JP4782407B2
JP4782407B2 JP2004349428A JP2004349428A JP4782407B2 JP 4782407 B2 JP4782407 B2 JP 4782407B2 JP 2004349428 A JP2004349428 A JP 2004349428A JP 2004349428 A JP2004349428 A JP 2004349428A JP 4782407 B2 JP4782407 B2 JP 4782407B2
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image
ultrasonic
irradiation
marker
tomographic image
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JP2006158413A (en
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義治 石橋
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東芝メディカルシステムズ株式会社
株式会社東芝
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  The present invention relates to an ultrasonic irradiation apparatus that performs treatment by focusing ultrasonic waves on a predetermined site inside a subject, and in particular, ultrasonic irradiation on a tomographic image of a subject in order to set a position to focus the ultrasonic waves. It is related with the ultrasonic irradiation apparatus which displays the marker image showing the aspect of this.

  Conventionally, surgical resection has been the main treatment for cancer treatment, and the physical and mental burdens of patients have been great. In addition, although drug therapy using anticancer drugs has been developed, its side effects have been a major problem.

  Therefore, in recent years, a treatment method called minimal invasive treatment (MIT) has been attracting attention. One example of minimally invasive treatment is hyperthermia therapy that heats cancer cells and leads to necrosis. This is a treatment method in which cancer cells are selectively killed by heating and maintaining the affected area at 42.5 ° C. or higher by utilizing the difference in heat sensitivity between tumor tissue and normal tissue. In particular, as described in Patent Document 1, for example, a method using ultrasonic energy having a high depth of penetration is considered for tumors in the deep part of a living body.

  Further, the above-mentioned warming treatment method is further advanced. As shown in Patent Document 2, for example, a treatment method in which the ultrasonic wave generated by the concave piezo element is focused on the affected area and heated to heat-denature necrosis is also considered. Yes. In the above treatment method, by focusing the energy of ultrasonic waves, it is possible to heat only a limited region having a width of about 1 to 3 mm to 60 ° C. or more and lead to heat-denatured necrosis within a few seconds. This technique is mainly being applied to liver tumors, breast tumors, brain tumors and urological tumors.

  Furthermore, recently, in order to eliminate the difficulty of using the fixed focus position, an ultrasonic focus is formed by electronic control (phased array) by using a plurality of ultrasonic generators and a phase-controllable drive source. For example, as described in Patent Document 3, a technique for obtaining an appropriate focal property by enlarging a focal spot size and lowering a focal peak pressure has been considered.

In any method of ultrasonic irradiation, as described in Patent Document 4 and Patent Document 5, an irradiation target is selected using an imaging apparatus such as an X-ray CT apparatus, an MRI apparatus, or an ultrasonic diagnostic apparatus. Display on a tomographic image. Then, targeting is performed by overlaying and displaying a marker indicating the focused position of the irradiation ultrasonic wave, a marker indicating the heating area indicating the area heated by ultrasonic irradiation, etc. on the irradiation target, and accurately aiming. After that, the process of irradiating with ultrasonic waves is performed. This improves the reliability of the irradiation effect and ensures safety. Furthermore, as described in Patent Document 6, a method has been proposed in which safety is further improved by displaying in advance a region to which the irradiation effect extends.
JP-A 61-13955 US Pat. No. 5,150,711 Japanese Patent Laid-Open No. 06-78930 Japanese Patent Application Laid-Open No. 02-114953 Japanese Patent Laid-Open No. 03-275050 JP 05-300910 A

  However, according to the methods described in Patent Documents 4 to 6 above, markers such as a range where the irradiation effect reaches and a focus position are superimposed on the irradiation target, and the success or failure of targeting between the target and the ultrasonic focus is achieved. However, the image display device such as CRT is generally distorted at the corners of the screen, so if you try to target at the end of the monitoring screen, the irradiation will be inaccurate. There is a drawback that the certainty of the effect and the safety are deteriorated.

  Furthermore, in the case of obtaining a tomographic image to be irradiated using an image diagnostic apparatus such as an ultrasonic diagnostic apparatus or MRI, image non-uniformity caused by an image acquisition method such as an ultrasonic diagnostic apparatus or MRI can be avoided. Absent. For example, in an ultrasonic diagnostic apparatus that performs a sector scan called a sector method or a convex method, the resolution of a generated image becomes worse as it goes deeper. In addition, the image quality of the generated image decreases as it goes to both ends due to the influence of quantization error caused by electronic scanning. Further, in MRI, due to the non-uniformity of the magnetic field, the image quality at the time of imaging toward the end of the gantry decreases. Therefore, depending on the location where the targeting is to be performed, the targeting is inaccurate and the reliability and safety of the irradiation effect are deteriorated.

  On the other hand, conventionally, markers were only superimposed and displayed at a certain brightness regardless of the tomographic image. Depending on the brightness of the tomographic image, it becomes difficult to distinguish it from the tomographic image or the tomographic image is difficult to see. In some cases, the targeting is inaccurate and the reliability and safety of the irradiation effect are deteriorated.

  In order to solve the above-mentioned problems, an ultrasonic irradiation apparatus according to claim 1 of the present invention includes an ultrasonic irradiation means for generating an ultrasonic wave and focusing it on a predetermined site in the subject, and an ultrasonic wave in the subject. A tomographic image acquisition means for acquiring a tomographic image including the predetermined part of the subject by transmitting a sound wave and acquiring an echo signal reflected in the subject; and a position on the tomographic image. An input means for performing an input to be designated; a marker image generating means for generating a marker image based on an input to the input means; a display means for displaying the tomographic image and the marker image superimposed; An area where the resolution of the tomographic image acquired by the tomographic image acquisition means is determined to be lower than a predetermined value is determined to have poor image quality, and the ultrasonic wave by the ultrasonic irradiation means is not focused on the area determined to have poor image quality. To control And having a control means.

According to the present invention, since the irradiation of the ultrasonic wave to the irradiation target site is controlled based on the quality of the tomographic image, the ultrasonic wave irradiation can be performed safely.

  Hereinafter, an exemplary embodiment of the present invention will be described with reference to the drawings.

  FIG. 1 is a configuration diagram showing a first embodiment of an ultrasonic irradiation apparatus according to the present invention. The ultrasonic irradiation apparatus according to this embodiment includes an ultrasonic applicator 10, ultrasonic irradiation control means 20, tomographic image acquisition means 30, control means 40, display means 50, and input means 60.

  The ultrasonic applicator 10 includes an ultrasonic wave generation element group 11 in which a plurality of divided vibrators are two-dimensionally arranged, a coupling material 12 for coupling the ultrasonic wave generation element group 11 and an object OBJ, a cup It consists of a film 13 that holds the ring material 12 and serves as a direct contact medium with the subject OBJ, and an ultrasonic probe 15 for tomographic images that is inserted into the central hole of the ultrasonic wave generation element group 11.

  The ultrasonic wave generation element group 11 is configured to irradiate ultrasonic waves in a designated frequency region toward the inside of the subject OBJ with the electric energy supplied from the ultrasonic wave irradiation control means 20. Furthermore, the coupling material 12 is used for the efficient propagation of ultrasonic waves to the subject OBJ, and realizes acoustic impedance matching between the ultrasonic wave generation element group 11 and the subject OBJ. In addition, the coupling material 12 also has a heat insulating effect for blocking the heat generated by the ultrasonic wave generating element group 11 and not transmitting it to the subject OBJ. Therefore, a cooling means 14 for releasing heat generated in the ultrasonic wave generation element group 11 is added to the opposite side of the ultrasonic wave generation surface of the ultrasonic wave generation element group 11, that is, the opposite side to the ultrasonic coupling material 12. It is.

  The tomographic ultrasound probe 15 is used to transmit and receive ultrasound for acquiring a tomographic image of the subject OBJ. Send and receive sound waves. Here, the tomographic ultrasound probe 15 may be provided so as to be rotatable with respect to the ultrasound generating element group 11 and the coupling material 12, whereby the ultrasound applicator 10 is fixed to the subject OBJ. Even in this state, the vicinity of the irradiation target part can be grasped three-dimensionally.

  Here, the ultrasonic wave generation element group 11 may be a plurality of ultrasonic transducers divided in the circumferential direction arranged in an annular ring shape, or a plurality of ultrasonic vibrations divided in an array shape. The child may be two-dimensionally arranged. Hereinafter, the former case is referred to as annular ring, and the latter case is referred to as a 2D array.

  The ultrasonic irradiation control means 20 includes a drive element group 21 for amplifying a signal waveform supplied to the ultrasonic generation element group 11 and a phase control means 22 for adjusting the phase of the signal waveform supplied to the ultrasonic generation element group 11. And waveform generating means 23 for generating waveform signals to be input to these. By performing these driving operations under the control of the control means 40, ultrasonic irradiation can be performed with a desired waveform, intensity, convergence and position.

  Here, when the ultrasonic wave generation element group 11 is an annular ring, the focus of the ultrasonic irradiation can be freely moved in the depth direction of the subject OBJ by the phase adjustment of the phase control means 22. In addition, when the ultrasonic wave generation element group 11 is a 2D array, two-dimensional phase adjustment is possible, so that the focal point of ultrasonic irradiation can be freely moved in three dimensions.

  The tomographic image acquisition unit 30 transmits a signal for transmitting the tomographic ultrasonic wave to the tomographic ultrasonic probe 15 and acquires the ultrasonic signal received by the tomographic ultrasonic probe. Thus, an ultrasonic tomogram image in the subject OBJ is constructed. The tomographic image acquisition ultrasonic wave is a pulse wave, and is transmitted in a predetermined direction in the subject from the tomographic image ultrasonic probe 15 by performing delay control. The diagnostic ultrasound reflected within the subject is received by the tomographic ultrasound probe 15 and subjected to delay processing, whereby the structure in the predetermined direction described above is imaged. By repeating this multiple times within a predetermined plane in the subject, the inside of the subject is scanned in a fan shape, and a tomographic image in the subject is obtained.

  On the other hand, the control means 40 comprehensively controls the entire apparatus. The functions of the control means 40 will be described below with a focus on the characteristic functions of this embodiment with reference to FIG. As shown in FIG. 2, the control means 40 has an image quality setting function 41, an image quality determination function 42, a focusing position setting function 43, a marker image generation function 44, and an image composition function 45.

  These functions will be specifically described below. First, the image quality setting function 41 sets various parameters of the tomographic image acquisition unit. Specifically, the various parameters include scanning line density, scanning range, depth range, scanning method, gain, focus control, and the like. When the operator operates the input unit 60, the operation information is transmitted to the image quality setting function 41, and various information is given to the tomogram acquisition apparatus, so that the image quality of the tomogram can be changed variously. .

  Next, the image quality determination function 42 determines the image quality in each part on the tomographic image based on various parameters relating to the image quality set by the image quality setting function 41. The image quality includes, in addition to resolution, display brightness, and color, image distortion depending on the structure of the monitor screen constituting the display unit 50. The distortion of the image is due to the curved monitor screen. When a CRT is used as the display means, the image becomes harder to see as it goes to the monitor end, and is perceived as distorted by the observer. .

  Further, the image quality determination function 42 detects at which position on the monitor screen the tomographic image is displayed, and detects image distortion information. The method of expressing the distortion information of the image may be, for example, two-stage information in which 5% from the edge of the image with respect to the entire screen is “distorted” and the other is “distorted”, or numerically expressed in stages. It may be something like

  Further, two-stage information representing the meaning of “good resolution” and “poor resolution” may be obtained with respect to the resolution, or may be numerically expressed in stages. Further, when the depth is set to 8 cm or more within 1 cm in depth, the resolution may be poor.

  Here, the image quality determination function 42 refers to the resolution information and the image distortion information described above, and determines whether each part on the tomographic image can be accurately targeted. Judgment criteria may be such that it is judged that accurate targeting cannot be performed when one of the resolution and the distortion of the image is information indicating "poor resolution" or "distortion", or both stages. Alternatively, a comprehensive determination may be made by comparing a predetermined value with a value obtained by adding or multiplying numerically digitized information. For example, if the accuracy required for alignment of the focusing position is set in advance using the input means 60 and the accuracy required for targeting is set to 2 mm, it is detected that separation of 2 mm or less is impossible. In such a case, it is determined that the targeting cannot be performed accurately.

  In addition, this determination may be performed by taking into account the quality of irradiation ultrasound focusing calculated from the irradiation ultrasound focusing position. For example, in the case of a 2D array, if the ultrasonic wave is focused in a direction greatly deviating from the normal of the surface formed by the ultrasonic wave generation element group, the quantization error becomes large and the focusing becomes blurred. Also, in the case of the annular ring, as the focusing position becomes deeper and when it is extremely shallow, the focusing of the irradiation ultrasonic wave becomes blurred. Furthermore, when the size of convergence and the irradiation time are set in advance, these pieces of information may be taken into consideration.

  Furthermore, the determination may be performed in consideration of the periphery of the irradiation target site. For example, when an important blood vessel is running in the vicinity of the irradiation target, it is necessary to eliminate the influence on the blood vessel, and the accuracy of targeting is required more severely. In addition, when there is a void in the void irradiation path, the acoustic impedance is greatly different between the void and the material portion, so that a large amount of energy is absorbed by reflecting the irradiated ultrasonic wave at the interface. On the other hand, when the irradiation target is a brain or the like, there are many important organs in the surrounding area, and thus more severe accuracy is required. Further, when the irradiation target is a breast, it is required not to destroy the outer shape, so that it is required to limit the irradiation to the minimum necessary region as much as possible.

  Therefore, by providing these pieces of information by input using the input unit 60, the accuracy necessary for the above-described targeting may be detected. In this case, for example, the input means 60 is used to mark a blood vessel or an empty space in the body while referring to a tomographic image, or an input means 60 that indicates a preset irradiation target such as “breast” and “head”. May be used to reflect the information on the operation of the focusing position setting function 43.

  Next, the focusing position setting function 43 is a function for setting a target that is a point for focusing the irradiated ultrasonic wave. This is done by the operator operating the input means 60 to specify an arbitrary position of the tomographic image, and the focusing position setting function 43 acquires the information. When the operator inputs a decision, information regarding the target position is stored in a built-in memory. When the irradiation start input is performed, this information is converted as phase information of each element of the ultrasonic wave generation element 11 and transmitted to the phase control means 22, thereby targeting ultrasound at an arbitrary position in the subject. Can be irradiated. This information may be information corresponding to one dimension only in the depth direction in the case of annular ringing, but is information corresponding to the three-dimensional direction in the case of 2D array.

  Here, based on the determination by the image quality determination function 42, the focusing position setting function 43 performs control so as not to accept the designation of the target position at the position where accurate targeting that is input to the input means cannot be performed. In that case, the operator is notified that the targeting is inaccurate.

  Next, the marker image generation function 44 is a function for generating a marker image for indicating a caution point on the tomographic image. Here, the marker image is a marker for indicating a region where the irradiation ultrasonic wave is focused as a focusing position, a marker for indicating a region affected by the heating by the ultrasonic irradiation as a heating region, It is assumed to include a straight line and a curve for indicating a path through which a sound wave propagates as a propagation path, a character image to be displayed on a tomographic image, and the like. The marker image generation function 44 acquires the position of the irradiation target on the designated tomographic image from the focusing position setting function 43 and generates a marker image corresponding to the position. This is synthesized in a form superimposed on the tomographic image by the image synthesis function 45 and displayed on the display means 50. Thereby, the operator can confirm the position of the target of the irradiation ultrasonic wave with reference to the tomographic image.

  Further, the marker image generation function 44 acquires the color or luminance at the position where various marker images are displayed on the tomographic image from the image quality determination function 42. Based on this information, the marker image generation function 44 generates a marker image so that the color or brightness differs from the tomographic image around the area where the marker image is displayed. In this case, the color, brightness, etc. may be set independently for each of the marker indicating the converging area, the marker indicating the heating area, the marker indicating the propagation path, or the character image. However, it may be changed for each pixel constituting the marker image.

  In addition, the marker image generation function 44 may acquire information on whether or not the position designated by the operator is a position that can be accurately targeted, and may generate a marker image reflecting the information. When it is determined that the targeting cannot be performed accurately, the marker image generation function 44 does not generate the marker image or notifies the fact that it cannot be accurately targeted. You may make it produce | generate the changed marker image.

  Hereinafter, an example of the operation of the present embodiment will be described with reference to FIGS. First, an overall outline of an operation example according to the present embodiment will be described with reference to FIG. 3, and then, an operation for setting a focusing position, which is an operation that characterizes the present invention, will be described in detail with reference to FIG. explain.

  In FIG. 3, first, as step S100, the ultrasonic applicator 10 is brought into contact with the subject OBJ. Here, if there are bubbles or the like between the ultrasonic applicator 10 and the subject OBJ, the acoustic impedance is not matched, and therefore, the ultrasonic waves are often reflected near the body surface, which is not preferable. Therefore, the acoustic consistency between the ultrasonic applicator 10 and the subject OBJ must be improved by using jelly or the like. Here, an ultrasonic applicator in a general ultrasonic irradiation apparatus must make a wide surface abut on the subject as compared with an ultrasonic probe or the like of an ultrasonic diagnostic apparatus. Therefore, since it is not easy to contact the ultrasonic applicator with the jelly sandwiched well, the operation of changing the position many times and bringing the ultrasonic applicator into contact should be avoided as much as possible. . At the same time that the ultrasonic applicator 10 is brought into contact with the subject OBJ, the tomographic image acquisition ultrasonic probe 15 is also brought into contact with the subject OBJ, so that the tomographic image of the subject OBJ can be obtained.

  Next, in step S200, various parameters for acquiring a tomographic image are set using the input means 60. In step S300, based on the set parameters, the image quality setting function 41 controls the tomographic image acquisition unit 30 to acquire a tomographic image. This is the same as the operation in a general ultrasonic diagnostic apparatus, and the operator performs adjustment so that the irradiation target is clearly depicted while referring to the actually obtained tomographic image. Further, adjustment is performed such that the irradiation target is clearly depicted by rotating the diagnostic ultrasonic probe 15 or the like.

  When the irradiation target is clearly depicted, the focused position of the irradiation ultrasonic wave is determined using the input device 60 in step S400. This operation will be described in detail later. Thereafter, in step S500, an irradiation start is input to irradiate the irradiation target with ultrasonic waves.

  Next, the operation for determining the focusing position in step S400 will be described in detail with reference to FIG. First, in step S <b> 401, the operator uses the input unit 60 to input for starting the setting of the focusing position. With this input, the focusing position setting function 43 is activated, and the focusing position is determined under the control of the focusing position setting function 43.

  In step S <b> 402, the operator uses the input unit 60 to input for specifying the position of the irradiation target on the tomographic image. The designation method is designated by instructing with a mouse, a light pen, or a trackball, tracing with a finger on the screen, or entering a numerical value such as a length or coordinates to designate a position or an area. In addition, when the irradiation target can be distinguished from the surroundings on the screen, the irradiation region may be determined using automatic contour detection. At that time, a function for manually correcting the automatically detected contour and a margin for the irradiation target are set in advance, and the automatic detection area is automatically added to the area including the margin to automatically become the irradiation target area. Or you may make it set manually. In this way, appropriate settings are possible without relying on the operator's judgment, which is preferable in terms of simplicity. Furthermore, in this step S402, the focused width of ultrasonic waves, the ultrasonic intensity, and the irradiation time may be set.

  In step S403, the focusing position setting function 43 acquires the image quality of the tomographic image at the currently designated position. The focusing position setting function 43 acquires a position on the designated tomographic image in accordance with the input in step S402.

  In step S404, the image quality determination function 42 determines the image quality of the tomographic image. The image quality determination function 42 is the relationship between the image quality parameter acquired by the image quality setting function 41, the specified position acquired by the focusing position setting function 43, and the distortion of the monitor that constitutes the display means stored in the memory built in advance and the display position. Based on the above, it is determined from the tomographic image quality at the position designated by the operator whether or not accurate targeting is possible, and information to that effect is transmitted to the focusing position setting function 43. In step S405, a determination is made based on this determination. If targeting is impossible, the operator is notified in step S406 that targeting is impossible, and the process returns to step S402, where the operator The setting will be redone.

  If it is determined that targeting is possible, in step S407, the marker image generation function 44 generates a marker image having a luminance corresponding to the image quality around the tomographic image on which the marker image is to be placed.

  The marker image generating function 44 is based on the position information of the designated position obtained from the focusing position setting function 43 and the image quality information of the tomographic image obtained from the image quality setting function 41, and the tomographic image on which the marker image is to be arranged. Get the image quality around the. Using this information, the color and brightness are adjusted so that the tomographic image and the marker image can be clearly identified when the marker image is superimposed on the tomographic image.

  When the marker image is generated, the image combining function 45 combines the marker image and the tomographic image and displays them on the display means 50 in step S408. The operator visually observes the tomographic image and the marker image displayed on the display means 50, and irradiates from the positional relationship between the irradiation target site represented in the tomographic image and the converging region or the heating region converging position represented as the marker image. Check if the ultrasonic focusing position is the specified location.

  If the designated location is acceptable, in step S409, input of the focusing position determination is performed using the input means 60, and in step S410, the designated position, irradiation time, and degree of focusing are stored in a built-in memory. The If it is considered that there is a risk that the heating region adversely affects other important parts of the irradiation target part, the process returns to step S402 and adjustment is performed again.

  Here, in this embodiment, since the determination is performed in step S405, if targeting is not possible, the marker image is not generated and the position adjustment is performed again. If S405 is skipped and targeting is impossible, a marker image for informing that effect may be generated and displayed. Even in this case, the position can be designated again by the determination in step S409.

  Next, the image quality determination performed by the image quality determination function 42 will be described in detail with reference to FIG. In the display means 50, a tomographic image 52 is displayed on the monitor screen 51 as shown in FIG. Since the tomographic image 52 is acquired by fan-shaped scanning by the tomographic image ultrasonic probe 15, the scanning mode can be schematically represented as a scanning line 53 in the tomographic image 52.

  Here, as described above, in ultrasonic irradiation, since normal tissue is not damaged, it is important to accurately heat the irradiation target region, and the focusing position is set to overlap with the irradiation target as accurately as possible. Must. Therefore, for example, when the accuracy of targeting is required in units of 1 mm, targeting with the necessary accuracy is impossible if the resolution of the tomographic image that serves as a guide for determining the focusing position is 2 mm. The image quality determination function 42 determines the image quality of the tomographic image from such circumstances.

  If the position on the tomographic image received by the focusing position setting function 43 by the operator's input means 60 is a very shallow point as indicated by A in the figure, the tomographic ultrasound probe 15 is used. In many cases, the ultrasonic waves from the side are not uniform and artifacts due to side lobes appear. Accordingly, since accurate targeting is difficult at a position such as A in the figure, the image quality determination function 42 determines that accurate targeting cannot be performed in such a region.

  Further, as shown by B in the figure, the laterally shifted point is an image obtained when the transducer of the tomographic image ultrasonic probe 15 is greatly delayed and the transmission ultrasonic beam for the tomographic image is covered. It is an area. Therefore, when the position on the tomographic image received by the focusing position setting function 43 by the operator's input means 60 is a point as indicated by B in the figure, each transducer of the ultrasonic probe 15 The quantization error depending on the size becomes large, and the image quality of the tomographic image is slightly inferior to the central portion. This situation is the same in the transmission of irradiation ultrasonic waves, and the convergence of irradiation becomes blurred as the irradiation region becomes the end. Accordingly, since accurate targeting is difficult at a position such as B in the figure, the image quality determination function 42 determines that accurate targeting cannot be performed even in such a region.

  Further, a case will be described in which the position on the tomographic image received by the focusing position setting function 43 by the operator's input means 60 is the lower end point indicated by C in the figure. Ultrasound for tomographic image acquisition is transmitted and received in a fan shape. That is, ultrasonic transmission / reception along the scanning line 53 shown in FIG. 5 is imaged. Therefore, the amount of information per unit area decreases as the distance from the center of the sector decreases, resulting in poor resolution. If the monitor screen 51 is a curved CRT or the like, it is difficult to see the tomographic image 52 and the marker image at the end of the monitor screen 51 such as the point C shown in the figure due to the curvature of the monitor screen 51. Become. Therefore, since accurate targeting is difficult at a position such as C in the figure, the image quality determination function 42 determines that accurate targeting is not possible even in such a region.

  That is, accurate targeting is possible at a position such as the converging position assignable region 54 shown in the figure. It should be noted that this converging position assignable region 54 may actually be displayed superimposed on the tomographic image 52. This is preferable in that accurate targeting can be performed easily because an area where accurate targeting can be performed can be grasped without the operator inputting input to the input means 60.

  In the present embodiment, the tomographic image acquisition means is based on ultrasonic transmission / reception, but is not limited thereto. For example, an MRI apparatus, an X-ray diagnostic apparatus, a CT apparatus, or the like may be used. Also in these cases, the image quality of the tomographic image is determined based on the image quality information such as the resolution according to the characteristics of the respective tomographic image acquisition means.

  Next, the marker image generated by the marker image generation function 44 will be described in detail with reference to FIG. Currently used medical tomographic images are almost in the form of brightness. Therefore, when the marker image is always generated with a constant luminance, it becomes very difficult to see if the luminance of the neighboring region where the marker image is displayed is close. As an example, consider a case where a tomographic image as shown in FIG. 6 is obtained. In the example of FIG. 6, α in the irradiation target region and β in the high luminance region are displayed in most of the low luminance regions. When a focusing position is designated in such a tomographic irradiation target area, a marker 55 indicating a heating area and a marker 56 indicating an irradiation ultrasonic wave propagation path are displayed at the positions shown in the figure. However, since the visibility may be poor if it is expressed with a constant luminance, the luminance of each marker image is adjusted in accordance with the luminance of the tomographic image. In the example of FIG. 6, the marker image is generated so that the marker image has low luminance in the vicinity of the high-brightness region β of the tomographic image, and the marker image has high luminance in the vicinity of the low-luminance region. This facilitates recognition of the marker image superimposed on the tomographic image, so that accurate targeting can be performed easily.

  In addition, the marker image may be generated by giving a constant multiple of luminance, for example, the luminance of the tomographic image at the position where the marker image is displayed is 100 times or 1/100. In this way, the tomographic image and the marker image are preferable in that the contour is emphasized by the difference in luminance and the marker image can be easily recognized.

  Further, the brightness indicating the heating area and the focusing area may be adjusted as a unit. In this case, the luminance information of the marker image is obtained by taking the average or maximum value of the luminance of the tomographic image of the region covered by the marker image indicating the heating region or the converging region, and multiplying this by a constant multiple. In this way, the form of the marker image can be grasped without being influenced by the display mode of the tomographic image.

  Furthermore, the operator may be able to adjust the brightness of the marker image by using the input means 60. In this case, the marker image indicating the heating area and the marker image indicating the irradiation ultrasonic wave propagation area can be adjusted independently, and the brightness can be adjusted so that the operator can easily see. The brightness of the marker image can be adjusted so that it can be easily seen.

  Further, as the heating to the irradiation target portion proceeds, the heating region gradually becomes brighter. Therefore, the brightness | luminance of a marker image may be adjusted according to the time to warm by storing the table of the brightness displacement by warming time beforehand. This is preferable in that it is difficult to see the marker image even if the tomographic image is altered during irradiation by ultrasonic irradiation.

  Further, the marker image generation function 44 may generate a marker image in which not only the luminance but also the color thereof are adjusted according to the tomographic image as the background. The marker image generation function 44 may simply give a red or blue color when the tomographic image is composed only of black and white luminance information. However, when the tomographic image includes color information such as color Doppler, As in the case of the luminance, the color of the marker image is adjusted according to the color of each point of the tomographic image as the background. In this way, even when the tomographic image is in color, it is preferable in that a marker image with good visibility can be displayed according to the display mode.

  Here, the display brightness and color of each of the marker image configurations, such as the marker image representing the convergence region, the marker image representing the heating region, and the marker image representing the propagation path of the irradiation ultrasonic wave, can be changed independently. good. For example, only the marker image representing the convergence area may be displayed according to the change in the form of the tomographic image, and the display may be performed with a certain luminance or color. This is preferable in that the control of the marker image generation function 44 is simplified.

Further, the marker image generation function 44 may change the brightness, color, shape, and the like based on the determination of the image quality determination function 42 by reflecting the accuracy of targeting at the designated position. If the specified position cannot be accurately targeted, the marker image is displayed in red, the shape of the marker image is changed from “○” to “×”, and the luminance is displayed from high to low. It is possible to notify the operator that accurate targeting cannot be performed.

  As described above, according to the present embodiment, it is possible to provide an ultrasonic irradiation apparatus that is accurate in targeting ultrasonic irradiation and can safely perform ultrasonic irradiation.

  According to the present embodiment, the image quality of the tomographic image serving as the guidance of the irradiation target region, the distortion of the displayed monitor screen, the irradiation condition of the irradiation ultrasonic wave, and the information on the vicinity of the irradiation target region of the subject, It is determined whether accurate targeting can be performed for the specified position. Furthermore, in this embodiment, the operator is informed of the determination result, or controlled so that the focusing position cannot be set at a position where accurate targeting cannot be performed based on the determination result. There is no ultrasonic irradiation based on targeting. Therefore, according to the present embodiment, it is possible to provide an ultrasonic irradiation apparatus that is accurate in targeting ultrasonic irradiation and can safely perform ultrasonic irradiation.

  Further, according to the present embodiment, the brightness and color of the marker image to be generated are adjusted according to the brightness and color of the tomographic image serving as the irradiation target guide. As a result, the marker image is displayed with brightness and color different from the brightness and color of the tomographic image displayed around the marker image. Therefore, it is easy to grasp the position of the marker image on the tomographic image, and it becomes easy to grasp the positional relationship between the irradiation target region and the region where heating should be avoided, the focused position of the irradiated ultrasonic wave, and the propagation path. The ultrasonic wave can be irradiated so as to be focused at a desired position through a proper propagation path. Therefore, according to the present embodiment, it is possible to provide an ultrasonic irradiation apparatus that is accurate in targeting ultrasonic irradiation and can safely perform ultrasonic irradiation.

The block diagram for showing the structure of the apparatus in embodiment which shows an example of this invention. The block diagram for showing the function structure of the control means in embodiment of FIG. The flowchart for showing the outline | summary of operation | movement of the apparatus in embodiment of FIG. The flowchart for showing the operation | movement for the determination of the focusing position in FIG. The figure for demonstrating the determination method of the image quality in embodiment of FIG. The figure for showing the example of a display of a marker image in the embodiment of FIG.

Explanation of symbols

DESCRIPTION OF SYMBOLS 10 Ultrasonic applicator 11 Ultrasonic wave generation element group 12 Coupling material 13 Film | membrane 14 Cooling means 15 Ultrasonic probe 20 for tomographic images Ultrasonic irradiation means 21 Drive element group 22 Phase control means 23 Waveform generation means 30 Tomographic image acquisition means 40 Control means 41 Image setting function 42 Image quality determination function 43 Convergence position setting function 44 Marker image generation function 45 Image composition function 50 Display means 51 Monitor screen 52 Tomographic image 53 Scanning line 54 Convergence position designation area 55 Marker 56 indicating a heating area Marker 60 input means for indicating irradiation ultrasonic wave propagation path

Claims (6)

  1. Ultrasonic irradiation means for generating an ultrasonic wave and focusing it on a predetermined site in the subject;
    A tomographic image acquisition means for acquiring a tomographic image including the predetermined portion of the subject by transmitting an ultrasonic wave in the subject and acquiring an echo signal reflected in the subject;
    Input means for performing input for designating a position on the tomographic image;
    Marker image generating means for generating a marker image based on an input to the input means;
    Display means for displaying the tomographic image and the marker image in a superimposed manner;
    An area in which the resolution of the tomographic image acquired by the tomographic image acquisition means is determined to be lower than a predetermined value is determined to have poor image quality, and the ultrasonic wave by the ultrasonic irradiation means is focused on the area determined to have poor image quality. Control means for controlling so as not to
    An ultrasonic irradiation apparatus comprising:
  2. The control means includes
    2. The ultrasonic irradiation apparatus according to claim 1, wherein when a position is designated by the input unit in an area where the image quality is determined to be poor, the designation is ignored .
  3. The control means includes
    2. The ultrasonic irradiation apparatus according to claim 1, wherein control is performed so that notification is made when a position is designated by the input means in an area where the image quality is determined to be poor .
  4. The marker image generating means
    When the position is designated by the input means in the area determined to be poor in image quality, and when the position is designated by the input means in the area determined to be good in image quality The ultrasonic irradiation apparatus according to claim 1, wherein the marker image is generated by changing at least one of luminance, color, and shape of the image .
  5. The control means includes
    The ultrasonic irradiation apparatus according to claim 1, wherein an image for indicating a region determined to have poor image quality is displayed on the tomographic image so as to be superimposed .
  6. The ultrasonic irradiation means includes
    A plurality of ultrasonic transducers arranged in a two-dimensional array;
    The ultrasonic irradiation apparatus according to claim 1, wherein the ultrasonic wave is focused at an arbitrary position by giving a delay to each of the ultrasonic vibrators .
JP2004349428A 2004-12-02 2004-12-02 Ultrasonic irradiation device Expired - Fee Related JP4782407B2 (en)

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Publication number Priority date Publication date Assignee Title
US20100056925A1 (en) * 2006-11-28 2010-03-04 Chongqing Ronghai Medical Ultrasound Industry Ltd. Ultrasonic Therapeutic Device Capable of Multipoint Transmitting
JP5036368B2 (en) * 2007-03-29 2012-09-26 富士フイルム株式会社 Medical image display apparatus and method
JP5156707B2 (en) * 2009-09-01 2013-03-06 日立Geニュークリア・エナジー株式会社 Ultrasonic inspection method and apparatus
KR20150107214A (en) 2014-03-13 2015-09-23 삼성메디슨 주식회사 Ultrasound diagnosis apparatus and mehtod for displaying a ultrasound image
JP6411185B2 (en) * 2014-11-19 2018-10-24 キヤノンメディカルシステムズ株式会社 Ultrasonic diagnostic equipment
JP6072206B2 (en) * 2015-11-25 2017-02-01 キヤノン株式会社 SUBJECT INFORMATION ACQUISITION DEVICE AND DISPLAY METHOD

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JPH11168669A (en) * 1997-12-03 1999-06-22 Hitachi Ltd Character signal inserting device
JP2000254137A (en) * 1999-03-11 2000-09-19 Olympus Optical Co Ltd Ultrasonic treatment device
JP2003219435A (en) * 2002-01-24 2003-07-31 Fuji Photo Film Co Ltd On-screen display device
JP4088126B2 (en) * 2002-09-09 2008-05-21 株式会社東芝 Ultrasonic therapy device
JP2004147719A (en) * 2002-10-29 2004-05-27 Toshiba Corp Ultrasonic wave irradiation apparatus
JP2004351230A (en) * 2004-09-09 2004-12-16 Olympus Corp Medical treatment system

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