JP4891651B2 - Ultrasonic diagnostic equipment - Google Patents

Description

The present invention relates to an ultrasonic diagnostic apparatus, and more particularly to an ultrasonic diagnostic apparatus that displays an instrument on a screen together with a living tissue.

  If an ultrasonic diagnostic apparatus is used, the state of the internal tissue of a living body can be displayed in real time as a two-dimensional tomographic image or a three-dimensional image. According to the ultrasonic diagnostic apparatus, it is possible to display the inside of the living body, which is difficult to see directly, as an image. Therefore, the ultrasonic diagnostic apparatus is also used when performing treatment or surgery. For example, as a method of treatment or diagnosis using an ultrasonic diagnostic apparatus, there is a method called ultrasonic guided puncture. This is a method of inserting a puncture needle while observing the state of a living body tissue on an ultrasonic image. According to this method, puncture can be performed while confirming the position of the affected tissue and the position of the puncture needle on the ultrasonic screen. The clinical benefit of this method is enormous. As an example of using an ultrasound diagnostic device for surgery, when operating a disease called a septal defect with a hole in the septum of the heart, the defect hole is sewn while observing the heart on an ultrasound image. There are new surgical methods to keep. In this surgical method, a suture instrument inserted into the body is displayed on an ultrasonic image. As described above, the ultrasonic diagnostic apparatus is used not only as an apparatus for measuring and diagnosing a living body, but also as an effective apparatus for treatment and surgery.

  Patent Document 1 discloses an image of a surgical instrument that shows a high reflectance by discriminating a low echo value range corresponding to a living tissue and a high echo value range corresponding to a metal object in a three-dimensional ultrasonic diagnostic apparatus. And the image of the living tissue are displayed simultaneously. The technique described in Patent Document 1 corrects the display of a metal object by projection calculation using a voxel value. However, Patent Document 1 does not allow control for changing the ultrasonic transmission / reception conditions. Patent Document 2 describes a technique related to an image analysis method for emphasizing a tissue of interest by performing texture analysis on image data obtained by transmitting and receiving ultrasonic waves.

JP 2003-164449 A JP 2000-316863 A

  When a surgical instrument is inserted into a patient's body and the operation is performed while confirming the position on the ultrasonic screen, the surgical instrument and its surroundings are displayed with high brightness as a whole on the ultrasonic screen. That is, the position of the surgical instrument is highlighted or displayed with a white tail. This is a phenomenon that occurs because a hard surgical instrument inserted into a living body exhibits high reflectivity with respect to ultrasonic waves. Such an image is a kind of artifact. The artifact is a virtual image that does not accompany the body tissue, but is displayed on the ultrasonic screen as if there is an object much larger than the actual size of the instrument. Therefore, there is a problem that the shape and position of the actual instrument cannot be clearly specified in image observation. The problem that the size and position of a hard instrument cannot be clearly displayed on the screen is a problem related to the operability, particularly at the time of puncturing, but also when imaging instruments other than puncturing.

  An object of the present invention is to provide an ultrasonic diagnostic apparatus that can clearly display an instrument even when the instrument is displayed as an ultrasound image.

  The present invention is a transmission / reception means for transmitting / receiving ultrasonic waves to / from a target tissue in which a hard instrument is inserted, and a means for controlling transmission / reception of the ultrasonic waves for imaging the target tissue at the first transmission / reception time. The first transmission / reception control means for setting the second transmission / reception condition for imaging the device during the second transmission / reception, and the two-dimensional or three-dimensional first data obtained during the first transmission / reception A combination processing unit that generates a combined data group by combining a group and the two-dimensional or three-dimensional second data group obtained at the time of the second transmission / reception, and based on the combined data group after the combining process; Display means for displaying a two-dimensional or three-dimensional ultrasonic image.

  According to the above configuration, when a two-dimensional or three-dimensional ultrasonic image is formed based on a reception signal obtained by the ultrasonic transmission / reception unit, the transmission / reception control unit switches and controls the transmission / reception conditions. As the transmission / reception conditions, it is possible to select a first transmission / reception condition suitable for imaging a target tissue and a second transmission / reception condition suitable for imaging a hard instrument. Therefore, in addition to the normal first transmission / reception condition, the second transmission / reception condition suitable for imaging a hard device is used in combination, and further, the data group obtained by the two transmission / reception conditions or the image composition processing based on them. By performing the above, the position and size of the instrument can be clearly displayed on the ultrasonic image after the synthesis process.

  Here, the hard instrument generally exhibits a high reflectance inside the living body, and specifically includes a surgical knife, forceps, a puncture needle, a suture instrument, and the like. The material of the instrument may be either metal or non-metal, but in particular, a metal instrument has a high acoustic impedance and a high reflectivity with respect to ultrasonic waves, so artifacts are likely to occur. The first data group and the second data group may be combined before the ultrasonic image is formed in the image forming unit, or after the ultrasonic image is formed. The timing for acquiring the first data group and the second data group is preferably in different time phases, but may be in the same time phase. Incidentally, the concept of the data group includes two-dimensional frame data and three-dimensional volume data. The concept of frame data includes transmission / reception frame data and display frame data.

  Preferably, the ultrasonic diagnostic apparatus includes partial compression processing means for performing partial compression processing on a partial data group corresponding to the instrument in the first data group or the synthesized data group.

  According to the said structure, the partial data group corresponding to an instrument can be compressed partially, ie, locally. Here, the partial data group corresponding to the device is a data group of a part of the first data group or a part of the composite data group. That is, the partial compression process may be applied before the synthesis process, or the partial compression process may be applied after the synthesis process. In any case, the brightness of the partial data group corresponding to the appliance, including artifacts, is reduced by the partial compression processing.

  Desirably, the transmission power in the second transmission / reception condition is smaller than the transmission power in the first transmission / reception condition. According to the said structure, the transmission power transmitted on 2nd transmission / reception conditions is reduced about transmission power. As the transmission power is reduced, the amplitude of the reflected wave received by the probe is reduced, that is, the luminance value of the data acquired as the second data group is reduced overall. Therefore, in the second data group, data based on reflected waves from an instrument that exhibits a high reflectance with respect to ultrasonic waves is usually dominant.

  Preferably, the reception gain in the second transmission / reception condition is smaller than the reception gain in the first transmission / reception condition. According to the above configuration, the reception gain in processing the reflected wave under the second transmission / reception condition is reduced. As the reception gain is reduced, the luminance of data acquired as the second data group is reduced. Therefore, since the luminance is reduced even for a data group based on a reflected wave from an instrument exhibiting high acoustic impedance with respect to the ultrasonic wave, the influence of the artifact can be reduced.

  Either one of the transmission power reduction process under the second transmission / reception condition and the reception gain reduction process under the second transmission / reception condition described above may be performed, or both may be performed simultaneously. As a result, it is only necessary to acquire an image that clearly represents the tissue and an image that clearly represents the instrument. In order to appropriately display the size and position of the appliance, it is desirable to appropriately adjust the degree of reduction of the transmission power and the reception gain to the optimum level in the second transmission / reception condition. In that case, both artificial adjustment and automatic adjustment are applicable.

  Preferably, the synthesis processing means includes a partial compression processing unit that partially compresses a partial data group corresponding to the instrument in the first data group, the first compressed data group, and the second data group. And an adding unit for generating the composite data group.

  According to the above configuration, first, partial data of the first data group is subjected to partial compression processing, that is, luminance compression processing. This partial compression processing is performed on the high-luminance partial data group (that is, partial data group) located in the vicinity of the instrument. That is, the partial data group that is the target of the partial compression processing is, for example, a portion where the size of the surgical instrument is displayed large due to the occurrence of an artifact. The first data group after partial compression and the second data group are added by the adder. The second data group is a data group acquired mainly from the instrument, and is a data group that can clearly specify the size and position of the instrument at the time of imaging. The second data group is added after the partial compression processing of the first data group is performed, so that the information on the instrument of the second data group is retained, and the size and position of the instrument in the composite data group are clearly identified. Can be specified. The synthetic data group can clearly grasp the size and position of the instrument, and the problem of artifacts in the partial data group corresponding to the instrument is apparently reduced, and the state of the living tissue other than the instrument is also clear. Is displayed.

  Preferably, the synthesis processing means includes an adding unit for adding the first data group and the second data group, and partial data corresponding to the appliance for the added data group output from the adding unit. And partial compression means for partially compressing the group to generate the composite data group.

  In the above configuration, the first data group is a data group acquired for observing a living tissue. For example, the first data group is a data group in which the influence of the artifact is greatly expressed and the instrument cannot be displayed clearly at the time of imaging. Yes. On the other hand, the second data group is a data group acquired for forming a clear image of the instrument, for example, a data group that can clearly specify the size and position of the instrument. The first data group and the second data group are first added and synthesized by the adder. Next, in the data group after the addition, the data group corresponding to the appliance is partially compressed, that is, luminance compressed. An ultrasonic image is formed on the basis of the composite data group partially luminance-compressed. Since the composite data group is partially compressed with respect to the partial data group corresponding to the instrument, it is possible to clearly grasp the size and position of the instrument on the ultrasonic image, and in some cases, an artifact in a normal case. It is also possible to make an organization that has been covered up by the surface appear.

  Preferably, it includes means for coloring the screen display color of the second data group to a color different from the display color of the first data group. According to the above configuration, the display color of the data group representing the device obtained by the second transmission / reception condition is displayed differently from the display color of the first data group in the ultrasonic image after the synthesis process. Thus, the part where the instrument is located or the part subjected to the partial compression process can be clearly recognized. For example, visual differentiation can be achieved by using color image information in addition to high and low luminance image information.

  As described above, according to the present invention, when an instrument is displayed on an ultrasound screen, the instrument can be clearly displayed, and the size and position of the instrument can be specified on the ultrasound image. Can do.

  DESCRIPTION OF EXEMPLARY EMBODIMENTS Hereinafter, preferred embodiments of the invention will be described with reference to the drawings.

  FIG. 1 is a schematic diagram of an ultrasound image projected on the display unit of the ultrasound diagnostic apparatus. In this example, the ultrasonic image 10 is a two-dimensional tomographic image of a patient's organ, and is an image obtained by bringing a sector scanning ultrasonic probe into contact with the patient's body surface. A puncture adapter 39 for guiding insertion of a puncture needle is attached to an ultrasonic probe used to display this image. The puncture needle is inserted into the body while being guided along the insertion path, and the state in the body is observed and recognized on the ultrasonic image 10. Since the ultrasonic image 10 is an image for observing an organ in the first place, a tomographic image of the organ is clearly shown in the sector scanning plane. However, in the ultrasonic image 10, image information that is not necessarily clear is also shown in a part of the sector scanning plane. The partial area 14 in FIG. 1 corresponds to that part. A partial region 14 having a form extending in an oblique direction schematically shows a region where an artifact is generated. A black region 12 inside the partial region 14 schematically shows a highlight display portion in which particularly strong artifacts are generated and glaring. The partial area 14 is caused by the puncture needle. For the sake of explanation, in FIG. 1, the region where the artifact is generated is shown as two regions for convenience, but in reality, a blurred luminance distribution is generated around the puncture needle. It should be noted that the actual shape of the puncture needle is difficult to identify on the image. A broken line 16 drawn from A1 to A2 in FIG. 1 is a broken line for explanation of FIGS. 5 and 8 described later.

  As described above, when a surgical instrument such as a puncture needle is inserted, a virtual image (artifact) that obstructs the observation of the puncture needle itself appears on the ultrasonic image, so that the puncture needle appears more than the actual shape. Large display. In puncturing, it is particularly important to identify and grasp the tip position of the puncture needle, but it is difficult to identify the position. Therefore, it is required to clearly display the shape and position of the puncture needle.

  FIG. 2 shows a principle diagram of the image composition method showing the first embodiment according to the present invention. Each of the four sector shapes (a) to (d) shown in FIG. 2 conceptually represents an ultrasonic image (corresponding to frame data) as a two-dimensional tomographic image. FIG. 2A shows the same image as the ultrasonic image of FIG. 1 described above. Here, FIG. 2A is an ultrasonic image obtained by applying normal ultrasonic transmission / reception conditions, that is, transmission / reception conditions for observing the internal tissue of a living body. Accordingly, as in FIG. 1, a portion where an organ is clearly displayed is dominantly displayed in the ultrasonic image, and a partial region 20 where an artifact is generated in a portion of the ultrasonic image is displayed. Is recognized. Incidentally, a high-intensity region 18 including a surgical instrument exists inside the partial region 20.

  FIG. 2B shows an ultrasonic image formed in a setting in which transmission / reception conditions are changed and transmission power is reduced. By reducing the transmission power, the artifact is also reduced, and the partial region 21 where the artifact is generated is still included, but the image 22 of the puncture needle is clearly imaged therein. Of course, as long as the image 22 of the puncture needle is obtained, a transmission / reception condition that substantially eliminates the artifact may be set. Since the ultrasonic image shown in FIG. 2 (b) is an image for clearly displaying the instrument, the organ is not always clearly displayed for the portion not included in the partial region 21 in FIG. 2 (b). There is no need to This is because when the ultrasonic image shown in FIG. 2 (b) is compared with the ultrasonic image shown in FIG. 2 (a), the organ is clearly displayed in FIG. 2 (a). In FIG. 2 (b), the organs are shown in contrast because they are not clearly displayed. Here, artifacts are reduced and a sharp image of the puncture needle is formed by a method of lowering the transmission power of ultrasonic waves, but the same effect can be obtained by lowering the reception gain for the received signal captured as a reflected wave. Ultrasonic images can be formed. Note that the selection order of the normal transmission / reception conditions and the weak transmission / reception conditions for puncture needle imaging can be determined as appropriate. Each transmission / reception condition may be set alternately for each beam or frame.

  FIG. 2C shows an ultrasonic image generated by performing image processing on the ultrasonic image shown in FIG. That is, in the ultrasonic image shown in FIG. 2A, first, the partial region 20 where the artifact is generated is specified. In this case, threshold processing or the like can be used as will be described later. Next, luminance compression processing is performed on the identified partial area 20. As a result, the high-luminance partial area 20 is compressed to become low-luminance, and apparently the occurrence of artifacts can be reduced. As a result, the partial region 24 has a relatively low luminance as a whole, and the luminance of the central region 23 is also reduced.

  FIG. 2D shows an ultrasonic image formed by synthesizing an ultrasonic image that clearly represents the shape of the puncture needle shown in FIG. 2B and a normal ultrasonic image shown in FIG. An acoustic image is shown. In FIG. 2, the addition and synthesis of ultrasonic images using the adder 30 is shown. As shown in FIG. 2D, the ultrasonic image after the addition synthesis has information of the image 22 corresponding to the puncture needle shown in FIG. That is, the partial region 21 including the image 22 corresponding to the puncture needle is directly superimposed on the partially compressed partial region 24 to form a partial region 28 shown in FIG. An image 29 corresponding to the puncture needle emerges and is displayed in the partial area 28, and the actual position and shape of the puncture needle are clearly shown on the ultrasonic image from the image 29 in comparison with the tissue. It is possible to specify. In other words, even if the artifact cannot be completely eliminated on the ultrasound image, the puncture operation can be performed safely if the shape of the puncture needle can be clearly imaged and the positional relationship between the tissue and the puncture needle can be clearly identified. it can. Image information of a tissue such as an organ included in the ultrasonic image shown in FIG. 2C is superimposed on the ultrasonic image shown in FIG. Therefore, it becomes easy to grasp the positional relationship between the puncture needle and the tissue by using the ultrasonic image of FIG. Of course, image processing may be performed so that artifacts can be substantially eliminated on the image.

  In the above description, the principle has been described using an example of a two-dimensional tomographic image. However, the image processing can actually be applied to the stage of frame data before image formation. It is also possible to apply the principle of image composition shown in this embodiment to processing of a three-dimensional image (that is, volume data). The same applies to other embodiments described later.

  FIG. 3 is a functional block diagram of an ultrasonic diagnostic apparatus to which the processing direction is applied. The system control unit 32 includes a CPU that integrally controls each unit in the ultrasonic diagnostic apparatus, and a storage unit that stores the first transmission / reception condition and the second transmission / reception condition as parameters. The system control unit 32 stores setting values input from the input unit 34.

  In this embodiment, the input unit 34 is configured by an operation panel having a keyboard and a trackball, and a user can make necessary settings for the system control unit 32 by using the operation panel. In this embodiment, in particular, the input unit 34 can be used to input and set ultrasonic transmission / reception conditions. That is, the setting values related to the first transmission / reception condition and the second transmission / reception condition can be set by the user. Incidentally, the transmission / reception conditions include ultrasonic transmission power, repetition frequency, reception gain, and the like.

  The system control unit 32 includes a transmission / reception control unit 36, and the transmission / reception control unit 36 controls operations of a transmission beam former 38 as a transmission unit and a reception beam former 42 as a reception unit, as will be described later. . In the present embodiment, the transmission / reception control unit 36 exists as one function of the system control unit 32, but it may be configured as an independent module. In the present embodiment, the transmission / reception control unit 36 performs the above-described first transmission / reception conditions (normal transmission / reception conditions for tissue image formation) and second transmission / reception conditions (particularly, transmission / reception conditions for clearly imaging the puncture needle). Are alternately set at a predetermined timing. Each transmission / reception condition may be variably set by the user as described above, or each transmission / reception condition may be automatically and adaptively set by image analysis or the like. Two beam data corresponding to at least two transmission / reception conditions are acquired for each beam direction. Of course, three or more transmission / reception conditions may be set.

  The probe 40 includes a 1D array transducer including a plurality of vibration elements. In the illustrated example, the probe 40 is in contact with the body surface of the living body. An ultrasonic beam (specifically, a transmission beam and a reception beam) 41 is formed by the array transducer, and a scanning plane 43 is formed by electronic scanning of the ultrasonic beam. Examples of the electronic scanning method include electronic linear scanning as well as electronic sector scanning as shown. The probe 40 may be provided with a 2D array transducer in which a plurality of vibration elements are two-dimensionally arranged, and an ultrasonic beam may be electronically scanned two-dimensionally to form a three-dimensional echo data capturing space. . It is also possible to form a similar three-dimensional echo data capturing space by mechanically scanning the 1D array transducer. In FIG. 3, r indicates the depth direction, and θ indicates the electronic scanning direction. In the present embodiment, the probe 40 has a puncture adapter 39 that is detachably attached to the main body thereof. The puncture adapter 39 is a mechanism for holding and guiding a puncture needle as an intracorporeal instrument. Specifically, the insertion path of the puncture needle is set in the scanning surface 43. In other words, the puncture adapter 39 guides the puncture needle so that the puncture needle can be observed on the tomographic image. Of course, the puncture needle may be guided from the direction intersecting the scanning plane. In FIG. 1, the tip of the puncture needle is delivered to the tissue of interest 45.

  In the transmission beam former 38, a plurality of transmission signals having a set voltage are generated in parallel under the control of the transmission / reception control unit 36. These transmission signals are each subjected to timing control, and then output to a plurality of vibration elements in the probe 40. As a result, a transmission beam is acoustically formed. When switching between the two transmission / reception conditions, the transmission power can be controlled by varying the voltage of the transmission signal. However, the transmission power may be varied by varying other parameters. The reflected wave from the living body is received by a plurality of vibration elements constituting the array transducer. A plurality of reception signals generated thereby are output in parallel to the reception beam former 42.

  The reception beam former 42 includes a plurality of A / D conversion circuits and a phasing adder. The plurality of reception signals input to the reception beam former 42 are converted from analog signals to digital signals by a plurality of A / D conversion circuits, respectively. A plurality of received signals after A / D conversion are phased and added by a phasing adder for electronically forming a received beam, and the received signal after phasing addition is used as beam data from the phasing adder. 44. In this embodiment, a digital beam former is used, but of course, an analog beam former may be used.

  A plurality of beam data corresponding to a plurality of beam directions constitute one frame data, which corresponds to one scanning plane. In this embodiment, two transmission / reception conditions are applied to each beam direction, that is, two types of beam data are acquired. In other words, two types of frame data are acquired. In this case, the two transmission / reception conditions may be alternately selected by switching in beam units, or may be alternately selected by switching in frame units. Or you may make it switch alternately by arbitrary units. It is also possible to maintain only the transmission power without switching the transmission power between the first transmission / reception condition and the second transmission / reception condition and switch only the reception gain. In that case, two pieces of data may be acquired in a time division manner, or two different reception gains are applied in parallel to the same reception signal, thereby acquiring two pieces of data simultaneously. May be. Alternatively, the repetition frequency may be reduced under the second transmission / reception condition. When the frequency is lowered, the resolution is lowered, but the occurrence of artifacts can be reduced. In any case, first frame data for tissue imaging and second frame data for puncture needle imaging as an instrument are acquired.

  The signal processing unit 44 processes the beam data output from the reception beam former. Here, for example, logarithmic amplification processing and reception gain adjustment processing are applied. The logarithmic amplification process is a process of performing logarithmic conversion on beam data in order to correspond to human visual characteristics. In addition to the process of adjusting the gain according to the diagnostic depth, the reception gain adjustment process includes a variable gain process for switching transmission / reception conditions in this embodiment. The gain for changing the two transmission / reception conditions can be changed in the signal processing unit 44 or in other units. The processed beam data is sent to the synthesis processing unit 46 at the next stage.

  The composition processing unit 46 includes a partial compression processing unit and an addition unit, which will be described in detail later. The synthesis processing unit 46 can be realized as dedicated hardware, a digital signal processor, or a software function executed by the CPU. The beam data may be output to an external PC, and the function of the composition processing unit 46 may be realized on the external PC. In such a case, the external PC also becomes a part of the ultrasonic diagnostic system. The combination processing unit 46 is alternately input with first frame data corresponding to the first transmission / reception condition and second frame data corresponding to the second transmission / reception condition. The synthesis processing unit 46 performs the image processing shown in FIG. 2, that is, performs synthesis processing on the frame data, and outputs the synthesized frame data to the image forming unit 48.

  In the present embodiment, the image forming unit 48 is configured by a digital scan converter (DSC). In other words, the image forming unit 48 has a coordinate conversion function and an interpolation processing function. Each frame data input to the image forming unit 48 (combined frame data in the combining processing mode according to the present embodiment) is converted into image data of a tomographic image. In this embodiment, the composition process is applied prior to image formation, but the composition process may be applied after image formation. The image data of the tomographic image is output to the display unit 50 as an image signal for display.

  The display unit 50 includes a display processor and a display. The display processor has an image composition function, a color composition function, and the like. A CRT or LCD is used as the display. When a coloring process is performed on the puncture needle portion in the second frame data, each frame data may be configured as color data prior to image synthesis. Alternatively, the display processor may recognize a region of the puncture needle portion and subsequently perform a coloring process on a portion corresponding to the region on the tomographic image. In any case, if display processing is performed so that the puncture needle portion or the portion to which partial compression processing is applied is visually identified, it becomes easy for the user to specify the data compression processing range on the image. .

  FIG. 4 is a functional block diagram of the synthesis processing unit 46. In this example, the composition processing unit 46 includes two memories 52 and 54, a partial compression processing unit 56, and an addition unit 58. The memories 52 and 54 are frame memories, and the memory 52 stores first frame data obtained by setting the first transmission / reception conditions. This first frame data corresponds to the image shown in FIG. The first frame data 52 is input from the memory 52 to the partial compression processing unit 56 at the next stage. In the partial compression processing unit 56, first, processing for specifying a partial region with high luminance is performed. In the present embodiment, the high-luminance partial region is specified by threshold processing that determines whether or not a certain luminance value is exceeded. Partial compression processing is performed on the identified partial area. This processing result corresponds to the image shown in FIG. On the other hand, the second frame data stored in the memory 54 is frame data obtained by setting the second transmission / reception condition. This corresponds to the image shown in FIG. In the adder 58, the first frame data subjected to the partial compression processing and the second frame data are added and synthesized. That is, two echo data (luminance values) on the same coordinates are added to obtain a new luminance value at the coordinates. The synthesized frame data 59 after the addition synthesis corresponds to the image shown in FIG. The combined frame data 59 is output to the image forming unit 48 shown in FIG. In the above configuration, the arrangement of the memory 52 may be omitted, and the arrangement of both the memories 52 and 54 may be omitted.

  Hereinafter, the specific contents of the above process will be described with reference to FIG. FIG. 5 shows a processing example of a one-dimensional received signal (beam data) for convenience of explanation, but the processing is actually applied to two-dimensional or three-dimensional data.

  (A) to (d) in FIG. 5 show signal waveforms. The horizontal axis indicates the magnitude of luminance. The horizontal axis indicates the distance from the ultrasound probe (corresponding to the broken line 16 (A1-A2) in FIG. 1). Specifically, (a) shows a signal waveform corresponding to the first transmission / reception condition, (b) shows a signal waveform corresponding to the second transmission / reception condition, and (c) shows the result after partial compression processing. The signal waveform is shown, (d) has shown the signal waveform after a synthetic | combination process.

  In (a), a threshold value TH1 is used to specify a high-luminance portion corresponding to the puncture needle, and a high-luminance portion is specified as a signal portion within a range 64a that exceeds the threshold value TH1. In addition, it is illustrated as ranges 62a and 66a other than the range 64a, which is a portion where the tissue is mainly imaged. The high brightness portion is apparently larger than the actual thickness or passage width of the puncture needle. The compression process is applied only to the high luminance part. That is, the portion in the range 64a is the compression processing target, and the other portions in the ranges 62a and 66a are stored as they are. The signal waveform after the partial compression processing is shown in (c). As indicated by the range 64c, the luminance is reduced in the range 64c. The signal waveform shown in (c) and the signal waveform shown in (b) are added as a whole (see reference numeral 78), thereby generating the signal waveform shown in (d). In this signal waveform range 64d, a waveform portion (see range 64b) that can clearly identify the puncture needle shown in (b) is superimposed on the waveform portion (see 64c) with reduced brightness, That is, although the artifact portion remains, its luminance is relatively reduced, and an image of the puncture needle is revealed in the interior with the background as a background. As a result, it is possible to form an image that represents a skeleton line inside the blurred portion.

  As described above, according to the image composition processing according to the first embodiment of the present invention, composite frame data, that is, a composite image is obtained so that the size and position of the puncture needle can be clearly grasped. Artifacts generated by the insertion of the puncture needle can reduce the influence on the image by reducing the luminance by partial compression processing. By superimposing data that clearly represents the skeleton of the puncture needle with respect to the partially compressed data, the skeleton of the puncture needle itself can be clearly imaged in relation to the tissue.

  FIG. 6 shows a principle diagram of an image composition processing method according to the second embodiment of the present invention. The image data shown in FIG. 6A corresponds to the image data shown in FIG. Reference numeral 82 indicates a portion where an artifact is generated, and reference numeral 80 indicates a high luminance portion. The image data shown in FIG. 6A occupies most of the image data that clearly shows the organs of the living body, but the other portions are occupied by high-luminance portions caused by artifacts. The image data shown in FIG. 6B corresponds to the image data shown in FIG. Reference numeral 83 denotes a portion where an artifact is generated. However, it is not so noticeable due to the application of the second transmission / reception condition. Reference numeral 84 denotes an image of the puncture needle. In this embodiment, the adder 86 adds the image data shown in (a) and the image data shown in (b), and then applies partial compression processing to the resultant composite image data. . That is, (c) shows composite image data, which shows that a clear portion of tissue and a portion where artifacts are generated can be discriminated based on the level of luminance even after the addition processing. . In the image data of FIG. 6C, reference numeral 87 indicates a portion where an artifact is generated, and reference numeral 88 indicates a high luminance portion. The image of the puncture needle is present in the high-luminance portion 88, but it is difficult to clearly identify the puncture needle itself on the image because of the influence of the high-luminance portion 88 as it is. Therefore, partial compression processing is performed on the composite image data. That is, a high-intensity part is specified and the process which reduces a brightness | luminance is applied with respect to the said part. The processing result is shown in (d). As indicated by reference numeral 90, although the artifact remains to some extent, the image of the puncture needle can be clearly expressed inside. In the image data shown in FIG. 6D, it is easy to grasp the position of the tissue, and therefore it is easy to grasp the positional relationship with the puncture needle. However, when the second embodiment is adopted, it is desirable that the luminance value of each coordinate is not saturated after the synthesis process. This is because, when the luminance difference between the image of the puncture needle and its surroundings disappears at the time of synthesis, the image of the puncture needle cannot be raised even if partial compression processing is applied. For this reason, for example, the dynamic range of the data after addition may be expanded.

  The synthesis processing unit 92 shown in FIG. 7 executes the second embodiment, and shows a specific configuration example of the synthesis processing unit 46 shown in FIG. The composition processing unit 92 includes two frame memories 94 and 96, an addition unit 98, and a partial compression processing unit 100. The two frame memories 94 and 96 store the first frame data and the second frame data, respectively, and the adder 98 generates synthesized frame data from them. The partial compression processing unit 100 specifies a high-luminance portion, that is, a compression target portion in the composite frame data, and applies a process of compressing the luminance to the portion. Thereby, the composite frame data 102 after the partial compression processing is obtained.

  FIG. 8 is a diagram illustrating specific contents of processing in the second embodiment, taking a one-dimensional signal waveform as an example. This corresponds to FIG. 5 showing the first embodiment. The signal waveform shown in (a) corresponds to the first transmission / reception condition, and the signal waveform shown in (b) corresponds to the second transmission / reception condition. When these signal waveforms are added by the adder 78, a signal waveform shown in (c) is obtained. On the other hand, the threshold TH2 is applied to identify the high-intensity portion 64c, and the partial compression processing is applied thereto. The processing result is a signal waveform shown in (d).

  Thus, according to the image composition processing according to the second embodiment of the present invention, composite image data that can clearly grasp the size and position of the appliance can be obtained. In the present embodiment, the luminance value becomes very large temporarily due to the addition and synthesis processing of the upper layer. Therefore, when the threshold value for specifying the high-luminance portion is determined, the luminance value is compared with the first embodiment. There is an advantage that the margin of the threshold setting range can be increased.

It is the figure which showed typically the state which displayed simultaneously the organ of a human body and the surgical instrument on the display screen of an ultrasonic diagnosing device. It is a principle figure of the image composition process concerning a 1st embodiment concerning the present invention. 1 is a block diagram showing an overall configuration of an ultrasonic diagnostic apparatus according to the present invention. It is a figure which shows the specific structural example of the synthetic | combination process part shown in FIG. It is the figure which showed typically the flow of the brightness | luminance compression process with respect to one beam data regarding the image processing which concerns on the 1st Embodiment of this invention. It is a principle figure of the image composition process concerning the 2nd Embodiment concerning this invention. It is a figure which shows the specific structural example of the synthetic | combination process part shown in FIG. It is the figure which showed typically the flow of the process of the luminance compression with respect to one beam data regarding the image processing which concerns on the 2nd Embodiment of this invention.

Explanation of symbols

  32 system control unit, 34 input unit, 36 transmission / reception control unit, 37 puncture needle, 38 transmission beam former, 39 puncture adapter, 40 probe, 41 ultrasonic beam, 42 reception beam former, 43 scanning plane, 44 signal Processing unit, 45 tissue of interest, 46 synthesis processing unit, 48 image forming unit, 50 display unit.

Claims (6)

A transmission / reception means for transmitting / receiving ultrasonic waves to / from a target tissue into which a hard instrument is inserted;
A means for controlling transmission / reception of the ultrasonic wave, wherein a first transmission / reception condition for imaging the target tissue is set during the first transmission / reception, and a second transmission / reception condition for imaging the instrument during the second transmission / reception. Transmission / reception control means for setting
A synthetic data group is generated by synthesizing the two-dimensional or three-dimensional first data group obtained at the time of the first transmission / reception and the two-dimensional or three-dimensional second data group obtained at the time of the second transmission / reception. Combining processing means to
Display means for displaying a two-dimensional or three-dimensional ultrasound image based on the composite data group after the composite processing;
Including
Transmission power in the second transmission and reception condition is minor than the transmission power in the first transmission and reception conditions,
An ultrasonic diagnostic apparatus comprising partial compression processing means for performing partial compression processing on a partial data group corresponding to the instrument in the first data group or the synthesized data group . The ultrasonic diagnostic apparatus according to claim 1,
The ultrasonic diagnostic apparatus, wherein a transmission repetition frequency in the second transmission / reception condition is lower than a transmission repetition frequency in the first transmission / reception condition. The ultrasonic diagnostic apparatus according to claim 1,
The ultrasonic diagnostic apparatus, wherein a reception gain in the second transmission / reception condition is smaller than a reception gain in the first transmission / reception condition. A transmission / reception means for transmitting / receiving ultrasonic waves to / from a target tissue into which a hard instrument is inserted;
A means for controlling transmission / reception of the ultrasonic wave, wherein a first transmission / reception condition for imaging the target tissue is set during the first transmission / reception, and a second transmission / reception condition for imaging the instrument during the second transmission / reception. Transmission / reception control means for setting
A synthetic data group is generated by synthesizing the two-dimensional or three-dimensional first data group obtained at the time of the first transmission / reception and the two-dimensional or three-dimensional second data group obtained at the time of the second transmission / reception. Combining processing means to
Display means for displaying a two-dimensional or three-dimensional ultrasound image based on the composite data group after the composite processing;
Including
The transmission power in the second transmission / reception condition is smaller than the transmission power in the first transmission / reception condition,
The synthesis processing means includes
A partial compression processing unit that partially compresses a partial data group corresponding to the instrument in the first data group;
An adder that adds the partially compressed first data group and the second data group to generate the combined data group;
An ultrasonic diagnostic apparatus comprising: A transmission / reception means for transmitting / receiving ultrasonic waves to / from a target tissue into which a hard instrument is inserted;
A means for controlling transmission / reception of the ultrasonic wave, wherein a first transmission / reception condition for imaging the target tissue is set during the first transmission / reception, and a second transmission / reception condition for imaging the instrument during the second transmission / reception. Transmission / reception control means for setting
A synthetic data group is generated by synthesizing the two-dimensional or three-dimensional first data group obtained at the time of the first transmission / reception and the two-dimensional or three-dimensional second data group obtained at the time of the second transmission / reception. Combining processing means to
Display means for displaying a two-dimensional or three-dimensional ultrasound image based on the composite data group after the composite processing;
Including
The transmission power in the second transmission / reception condition is smaller than the transmission power in the first transmission / reception condition,
The synthesis processing means includes
An adder for adding the first data group and the second data group;
Partial compression means for partially compressing a partial data group corresponding to the appliance with respect to the data group after addition output from the addition unit, and generating the composite data group;
An ultrasonic diagnostic apparatus comprising: The ultrasonic diagnostic apparatus according to claim 1,
An ultrasonic diagnostic apparatus comprising display processing means for making a display color of the second data group different from a display color of the first data group.

Images