Abstract:
An objective of the present invention is to provide an ultrasound system which can correct a positive-negative asymmetry in pulse inversion (PI) and obtain a high-image quality ultrasound image. To carryout an asymmetry correction of a transmission assembly circuit comprising an oscillation adjustment amplifier ( 10 ) and an ultrasound oscillator array ( 90 ), correction data obtained in a calibration mode is stored in a correction memory ( 46 ), and positive-negative asymmetry of an overall receiving assembly circuit comprising a computation unit ( 45 ) is corrected in a diagnostic mode of the device using the correction data.

Description:
TECHNICAL FIELD 
       [0001]    The present invention relates to an ultrasound system, and specifically, the technology aiming at high image quality of the ultrasound system utilizing a pulse inversion method. 
       BACKGROUND ART 
       [0002]    The pulse inversion (PI) method has been known as the method for achieving high image quality of the ultrasound image. The PI method is called phase inversion method as the technique for ultrasound imaging with a harmonic content (harmonic) by utilizing nature of the ultrasound resulting from irradiating the living body organ with ultrasound at the single frequency. Specifically, upon ultrasound irradiation, the fundamental wave of the reflection ultrasound reflects at the same frequency with the same polarity as the irradiated ultrasound. On the contrary, the harmonic content of the reflection ultrasound reflects with monopolar regardless of polarity of the irradiated ultrasound. More specifically, a first reflection ultrasound (including the first fundamental wave content and the first harmonic content) as a result of irradiation of the first transmission waveform (positive electrode) is received, and a second reflection ultrasound (including the second fundamental wave content and the second harmonic content) as a result of irradiation of the second transmission waveform (negative electrode) is received, which has been derived from reversing polarity of the first transmission waveform (or phase shift at 180°). Addition of the first and the second reflection ultrasounds will offset the first and the second fundamental wave contents, making the first and the second harmonic contents doubled. Consequently, the PI method is carried out on the assumption that the sum of the first transmission waveform (positive electrode) and the second transmission waveform (negative electrode) is zero with respect to those frequency contents such as the fundamental wave and the harmonic content. If the assumption is ineffective, image quality is deteriorated, or in some cases, artifact (false image) is generated. In the transmission-reception circuit system of the actual configuration of the device, the positive-negative asymmetry (the sum of the first and the second transmission waveforms is not zero) is caused by various factors. 
         [0003]    Various proposals for retaining the positive-negative symmetry have been made by, for example, Patent Literature 1 disclosing the transmission circuit suitable for carrying out the PI method, Patent Literature 2 disclosing structure of the oscillator for efficiently receiving the harmonic content, and Patent Literature 3 disclosing the method of processing the reception signal utilizing the filtering method. 
       CITATION LIST 
     Patent Literature 
       [0000]    
       
         PTL 1: Japanese Unexamined Patent Application Publication No. 2007-117668 
         PTL 2: Japanese Unexamined Patent Application Publication No. 2002-248100 
         PTL 3: Japanese Unexamined Patent Application Publication No. 2002-369817 
       
     
       SUMMARY OF INVENTION 
     Technical Problem 
       [0007]    Generally in the transmission circuit which drives the oscillator for ultrasound transmission, the respective waveforms of the positive/negative electrodes become asymmetrical because of characteristic differences in the P-type and N-type transistors that constitute the circuit. In consideration of variation in the parts and elements, it is difficult to compensate for the positive-negative asymmetry of a plurality of transmission circuits in the ultrasound system and the ultrasound probe. Since the ultrasound oscillator as the load of the transmission circuit transmits the ultrasound in accordance with transmission waveform of the positive/negative electrode from the transmission circuit, and the ultrasound oscillator exhibits nonlinear characteristic, asymmetry of the transmission waveform cannot be compensated. Furthermore, it is difficult for the unit for computing the reception signal to compensate for the asymmetry owing to characteristic of the transmission circuit, and nonlinearity of the oscillator. 
         [0008]    It is an object of the present invention to provide an ultrasound system, and a method, and an ultrasound probe, which ensure acquisition of the ultrasound image with high quality utilizing the pulse inversion method by solving the aforementioned problems. 
       Solution to Problem 
       [0009]    The aforementioned object is accomplished by the present invention which provides an ultrasound system including a transmission unit which transmits a first transmission signal and a second transmission signal obtained by polarity inversion of the first transmission signal, an ultrasound probe which transmits an ultrasound based on the first transmission signal and the second transmission signal from the transmission unit, and receives an ultrasound as a reflection ultrasound, a reception unit which receives a first reception signal and a second reception signal corresponding to the first transmission signal and the second transmission signal based on the reflection ultrasound received by the ultrasound probe, and a storage unit which stores correction data for correcting a positive-negative asymmetry based on an addition result of the first reception signal and the second reception signal in a calibration mode. The reception unit executes a correction computation using the addition result of the first reception signal and the second reception signal, and the correction data stored in the storage unit in a diagnostic mode. 
         [0010]    The object is accomplished by the present invention which provides an ultrasound diagnostic method including the steps of transmitting a first transmission signal and a second transmission signal obtained by polarity inversion of the first transmission signal from an ultrasound probe, receiving a reflection ultrasound by the ultrasound probe, which has been transmitted based on the first transmission signal and the second transmission signal, and retaining an addition result derived from adding a first reception signal and a second reception signal corresponding to the first transmission signal and the second transmission signal based on the received reflection ultrasound in a calibration mode as correction data for correcting a positive-negative asymmetry, and carrying out a correction computation utilizing the addition result of the first reception signal and the second reception signal, and the retained correction data in a diagnostic mode. 
         [0011]    The object is accomplished by the present invention which provides an ultrasound probe including a connector capable of connecting a transmission unit for transmitting a first transmission signal and a second transmission signal obtained by polarity inversion of the first transmission signal, and a reception unit for receiving a first reception signal and a second reception signal corresponding to the first transmission signal and the second transmission signal, an ultrasound probe array which transmits the ultrasound based on the first transmission signal and the second transmission signal from the transmission unit, and receives an ultrasound as a reflection ultrasound, and a storage unit which stores correction data for correcting a positive-negative asymmetry based on an addition result of the first reception signal and the second reception signal in reference to the reflection ultrasound in a calibration mode. 
       Advantageous Effects of Invention 
       [0012]    The present invention ensures high quality ultrasound image utilizing the pulse inversion (PI) method. 
     
    
     
       BRIEF DESCRIPTION OF DRAWINGS 
         [0013]      FIG. 1  is a view representing an exemplary structure of an ultrasound transmission-reception circuit according to a first embodiment. 
           [0014]      FIG. 2  is a view representing a structure of a computation unit according to the first embodiment. 
           [0015]      FIG. 3  is a view representing a structure of the computation unit according to a second embodiment. 
           [0016]      FIG. 4  is a view representing a structure including an ultrasound system and an ultrasound probe according to a third embodiment. 
           [0017]      FIG. 5  is a flowchart representing an example of an operation of the ultrasound system according to the respective embodiments. 
           [0018]      FIG. 6  is a flowchart representing another example of the operation of the ultrasound system according to the respective embodiments. 
           [0019]      FIG. 7  is a view representing an exemplary structure of an oscillator of a two dimensional (2D) array probe according to a fourth embodiment. 
           [0020]      FIG. 8  is a view representing an example of a user adjustment panel according to the respective embodiments. 
           [0021]      FIG. 9  is a view representing an exemplary structure of a transmission-reception circuit of a generally employed ultrasound system. 
       
    
    
     DESCRIPTION OF EMBODIMENTS 
       [0022]    Before explanation of the respective embodiments according to the present invention, described is an exemplary structure of the transmission-reception circuit of a generally employed ultrasound system capable of carrying out the pulse inversion (PI) method referring to  FIG. 9 . Referring to the drawing, upon instruction of diagnosis to a control circuit  50  via a user control unit  70 , the control circuit  50  constituted by the central processing unit (CPU) follows the instruction by outputting a transmission reference signal to a transmission waveform control unit  40 , which is a base of the ultrasound transmission signal to an ultrasound oscillator array  90 . Transmission circuits  10 - 1  to  10 - n  output the transmission signal for the required voltage amplitude signal in reference to the transmission reference signal. The transmission signal is applied to ultrasound transducer elements  80 - 1  to  80 - n  of the ultrasound oscillator array  90  via transmission lines  100 - 1  to  100 - n . Then the living body as the subject is irradiated with the ultrasound signal via a not shown ultrasound jelly used upon ultrasound irradiation. The reflection ultrasound signal reflecting from the living body is received by the ultrasound transducer element  80 - 1  to  80 - n  of the ultrasound oscillator array  90  as well, and further sent to a computation unit  45  via reception lines  110 - 1  to  110 - n , reception circuits  20 - 1  to  20 - n , and analog-digital converters  30 - 1  to  30 - n . The signal is subjected to a predetermined computation in the computation unit  45 , and the result is sent to the control circuit  50  so as to display the ultrasound in-vivo image on a display unit  60 . 
         [0023]    The aforementioned PI method involves the operation of the components from the transmission waveform control unit  40  to the computation unit  45  subsequent to the control circuit  50  as described above. Description in the respective embodiments will be made with respect to the operation carried out by the components from the transmission waveform control unit  40  to the computation unit  45 . The transmission waveform control unit  40  and the computation unit  45  are illustrated in simplified manner for explanation purpose, which are not intended to limit the number of function blocks. This applies to the respective embodiments as described below. In the specification, two operation modes including a calibration mode and a diagnostic mode will be described as the operation mode of the ultrasound system. The calibration mode refers to the operation mode for irradiating the predetermined reflection medium with the positive-negative ultrasound based on the PI method prior to the diagnosis so as to acquire correction data for correcting the positive-negative asymmetry. The diagnostic mode refers to the operation mode for irradiating the living body as the subject with the ultrasound so as to acquire the in-vivo ultrasound image. In the description according to the invention, explanation will be made with respect especially to the case for acquiring the ultrasound image (video image) utilizing the PI method. Hereinafter, the modes for carrying out the present invention will be described referring to the drawings. Structures and operations of the respective embodiments will be described hereinafter. The specific explanations of the calibration mode and the diagnostic mode will be made collectively in the latter part of a fourth embodiment. 
       First Embodiment 
       [0024]    A first embodiment relates to an ultrasound system which includes a transmission unit which transmits a first transmission signal and a second transmission signal obtained by polarity inversion of the first transmission signal, an ultrasound probe which transmits an ultrasound based on the first transmission signal and the second transmission signal from the transmission unit, and receives an ultrasound as a reflection ultrasound, a reception unit which receives a first reception signal and a second reception signal corresponding to the first transmission signal and the second transmission signal based on the reflection ultrasound received by the ultrasound probe, and a storage unit which stores correction data for correcting a positive-negative asymmetry based on an addition result of the first reception signal and the second reception signal in a calibration mode. The reception unit executes a correction computation using the addition result of the first reception signal and the second reception signal, and the correction data stored in the storage unit in a diagnostic mode. 
         [0025]    A series of structures correct the positive-negative asymmetry including characteristic changes resulting from a transmission signal (electric signal) output from the transmission circuit as the transmission unit, an ultrasound oscillator (electricity-ultrasound interconversion) as the ultrasound probe, and a reception circuit as the reception unit. 
         [0026]    Referring to the structure shown in  FIG. 1 , the control circuit  50  controls the transmission waveform control unit  40  for applying a transmission signal to the transducer elements  80 - 1  to  80 - n  constituting the ultrasound oscillator array  90  via the transmission circuits  10 - 1  to  10 - n.    
         [0027]    Transmission ultrasounds  200 - 1  to  200 - n  generated from the respective transducer elements  80 - 1  to  80 - n  of the ultrasound oscillator array  90  are radiated to an irradiation subject via a medium  95  such as the ultrasound jelly used for ultrasound irradiation, which is applied between the ultrasound oscillator array  90  and the body surface in ultrasound inspection. The reflecting ultrasounds  210 - 1  to  210 - n  from the irradiation subject are received by the respective transducer elements  80 - 1  to  80 - n  of the ultrasound oscillator array  90  via the medium  95  in the similar way. The received reception signal is input to the computation unit  45  via the reception circuits  20 - 1  to  20 - n , and analog-digital converters (ADC)  30 - 1  to  30 - n . In this case, the medium  95  in the form of ultrasound jelly or gel serves to prevent scattering of air between the ultrasound oscillator array  90  and the body surface. 
         [0028]      FIG. 2  is a view representing an example of the inner circuit structure of the computation unit  45  in the reception circuit system according to the embodiment. The first reception data (positive electrode)and the second reception data (negative electrode) are accumulated in reception data buffers  41 - 1 ,  41 - 2 , respectively, which are added in an adder  42 . In the diagnostic mode, correction is carried out using the correction value preliminarily stored in a correction memory  46  in the calibration mode. The correction value stored in the correction memory  46  is subjected to gain adjustment by a gain adjuster  44  in accordance with depth information of the living body in the diagnostic mode. The embodiment is configured to easily execute the aforementioned process by changing the digital processing unit subsequent to the ADCs  30   a  to  30   n  of the main body of the device. 
       Second Embodiment 
       [0029]    A computation unit in this embodiment is differently structured from the computation unit  45  of the ultrasound system as described in the first embodiment.  FIG. 3  shows a structure of the computation unit  45  as a modified example in the reception circuit system which has been described in the first embodiment. Referring to the drawing, only the structure different from the one shown in  FIG. 2  will be described. In the calibration mode, the structure is designed to subject the addition data from the adder  42  to Fourier transformation carried out by an FFT processing unit  47 . The resultant data are stored in the correction memory  46 . In the diagnostic mode, the correction data in the correction memory  46  are read, and inverse Fourier transformed by an inverse FFT processing unit  48 . The resultant data are sent to a correction computation unit  43  via an interpolation computation/gain adjuster  49  for correction. 
         [0030]    The embodiment is configured to correct the reception data utilizing fast Fourier transformation (FFT) and inverse fast Fourier transformation (inverse FFT) so that the data with respect only to frequency and magnitude are stored. The embodiment provides the advantage of smaller memory area than that of the first embodiment. In other words, the first embodiment is configured to store data in a time direction, requiring storage of enormous data in accordance with reception time and ADC sampling frequency in the ADC  30 , or partially interpolated data. This embodiment is configured to store the data in accordance only with the frequency and magnitude, which makes it possible to reduce the memory area smaller than the first embodiment. 
       Third Embodiment 
       [0031]    An ultrasound system according to this embodiment is configured to have the correction memory for storing the aforementioned correction data disposed at the side of the ultrasound probe. 
         [0032]      FIG. 4  shows an exemplary structure of the third embodiment. Referring to the drawing, the same components as those described in the first embodiment are designated with the same signs as shown in  FIG. 1 , and explanations thereof, thus will be omitted. An ultrasound system  300  (main body) and a connector box (BOX)  53  are connected with connectors  51 ,  52 . The ultrasound oscillator array  90  in the overall structure shown in  FIG. 1  is disposed at the side of an ultrasound probe  56  in the drawing. 
         [0033]    The correction memory  54  for storing the correction data as described above is disposed in the connector BOX  53 . The ultrasound reception signal and the correction data are sent to the computation unit  45  of the ultrasound system (main body) via the connectors  51  and  52  so that the correction computation is executed. As the aforementioned process is similar to the one described in the former embodiments, the explanation will be omitted. The connector BOX  53  and the ultrasound probe  56  are connected via a cable  55 , which may be collectively called the ultrasound probe. For the computation unit  45 , it is possible to employ the corresponding structure according to either the first or the second embodiment. 
         [0034]    The structure according to this embodiment necessitates no addition of the memory at the main body side of the ultrasound system to be adapted to the newly developed ultrasound probe. As a result, it is possible to allow the previously purchased ultrasound system to easily realize the high quality image. The device of the aforementioned type includes components for identifying the type of the ultrasound probe such as the microcomputer (MCU) and FPGA (field-programmable gate array) in the connector BOX. Those components may be commonly used with the correction memory  54 . It is therefore possible to provide the ultrasound probe with correction memory at lower costs. 
       Fourth Embodiment 
       [0035]    This embodiment describes a 2D array probe of the ultrasound system.  FIG. 7  is a schematic front view of the 2D array probe of the embodiment. Referring to  FIG. 7 , the probe according to the embodiment is constituted by a group of sub-arrays each formed of a plurality of (nxm) oscillators. In the case where the (nxm) oscillators are arranged in 2D array to form the probe, the integrated circuit is connected adjacently to the 2D array. Such structure makes it possible to compensate for the symmetry using the correction data with smaller number than that of the oscillators. The 2D array requires the integrated circuits by the number corresponding to that of oscillators. The integrated circuits allow dispersion between adjacent circuits to be lessened, which allows execution of the calibration mode through restriction of the number of circuits to those at the respective corners and at the center, or thinning out of every other sub-arrays among plural (nxm) sub-arrays. Those thinned-out sub-arrays are subjected to the process to share the correction data acquired by the adjacent oscillator. This makes it possible to execute the correction process equivalently to all the oscillators. 
         [0036]    The method of correcting the positive-negative asymmetry, which is carried out in the above-described ultrasound system according to the embodiments will be explained. The ultrasound system according to the respective embodiments includes two operation modes, that is, the calibration mode and the diagnostic mode. The operation flow of the calibration mode executed by the manufacturer or the user of the ultrasound system will be explained referring to  FIG. 5 . The manufacturer of the device acquires the correction data by following the operation flow executed in the calibration mode upon shipment inspection of the ultrasound system. Meanwhile, the user is allowed to follow the operation flow to acquire the correction data. 
         [0037]      FIG. 5  represents an example of the operation flow for acquisition of the correction data stored in the correction memory according to the respective embodiments as described above. Signs in the parenthesis may be referred to  FIG. 5 , and other signs may be typically referred to  FIGS. 1 and 3 . Referring to  FIG. 5 , upon start (START) of the acquisition flow under control of the control circuit  50 , N=1 is set in a not shown counter so as to output a transmission reference signal to the transmission waveform control unit  40  shown in  FIG. 1 , which is a base of a first ultrasound transmission signal to the first transducer element  80 - 1 . Then the first transmission waveform is applied to the first transducer elements  80 - 1  via a first transmission circuit  10 - 1  (S 1 ). At this timing, the transmission waveform control unit  40  is controlled not to output the transmission reference signal to the second to the nth transmission circuits  10   b  to  10   n , or the second to the nth transmission circuits l 0   b  to  10   n  are controlled not to output the signal. 
         [0038]    Referring to  FIG. 5 , in the calibration mode, the living body is not irradiated with ultrasound. The transmitted ultrasound is reflected and attenuated by the medium  95  applied onto the surface of the ultrasound oscillator array  90  as shown in  FIG. 1  so as to allow the reception circuit systems to detect the received ultrasound. In other words, a first reflection ultrasound (ultrasound echo)  210 - 1  from the medium  95  is received by the first ultrasound transducer element  80 - 1  (S 2 ), and input to the computation unit  45  via a first reception circuit system line  110 - 1 , the first reception circuit  20 - 1 , and the first ADC  30 - 1  so that the reflected ultrasound is detected (S 3 ). The first reflection ultrasound signal is stored in the reception data buffer  41 - 1  in the computation unit  45  (S 4 ). 
         [0039]    Likewise the above-described case, the transmission waveform control unit  40  outputs the transmission reference signal as a base of a second ultrasound transmission signal to the first transducer element  80 - 1  for generating a second transmission waveform via the first transmission circuit  10 - 1 . It is applied to the first ultrasound transducer elements  80 - 1  of the ultrasound oscillator array  90  so that the detection data are stored in the data buffer  41 - 2  (S 5  to S 8 ). The stored detection data are added by the adder  42  (S 9 ), and a first addition result with respect to N=1 is stored in the correction memory  46  (S 10 ). In the case where N oscillators, for example,  64  oscillators in a single array constitute the 1D array, the same process steps are repeatedly executed until N reaches 64 (S 1  to S 10 ). Then the calibration mode ends (S 11 , S 12 ). The second transmission waveform is the one derived from polarity inversion of the first transmission waveform, or the phase shift at 180° from the first transmission waveform based on the PI method. The correction data may be acquired by activating the system constituted by a second transmission circuit  10 - 2 , a second transducer element  80 - 2 , and a second reception circuit  20 - 2  in the case of N=2, or the system constituted by a third transmission circuit  10 - 3 , a third transducer element  80 - 3 , and a third reception circuit  20 - 3  in the case of N=3. The aforementioned step is intended to eliminate the influence of the adjacent oscillator, resulting from operation of a plurality of oscillators. The aforementioned correction data flow in the calibration mode is a mere example. In the case of the 1D array constituted by the single array of  64  oscillators, it is possible to execute  2 -system operation. For example, the system (N=1) including the first transmission circuit  10 - 1 , the first transducer element  80 - 1 , and the first reception circuit  20 - 1  may be operated simultaneously with the system including the 33rd transmission circuit  10 - 33 , the 33rd transducer element  80 - 33 , and the 33rd reception circuit  20 - 33 . Similarly, the system (N=2) including the second transmission circuit  10 - 2 , the second transducer element  80 - 2 , and the second reception circuit  20 - 2  may be operated simultaneously with the system including the 34th transmission circuit  10 - 34 , the 33rd transducer element  80 - 33 , and the 33rd reception circuit  20 - 33 . If the oscillators are not arranged adjacently, they are less influenced by the other oscillator. Therefore, simultaneous operation of a plurality of discrete systems ensures reduction in the time for the correction data acquisition in the calibration mode. 
         [0040]    Execution of the operation flow in the calibration mode as described above allows acquisition of the correction data for correcting the positive-negative asymmetry including characteristic changes resulting from a transmission signal waveform (electric signal) of the transmission circuit output, the oscillator (electricity-ultrasound interconversion), and the reception circuit in a series of transmission-reception circuit systems. Upon acquisition of the correction data by the user through execution of the operation flow shown in  FIG. 5 , it is possible to acquire the correction data with high accuracy adapted for change in user&#39;s setting of the transmission ultrasound power and frequency. As the user performs the correction in using the device, the highly accurate correction data may be acquired corresponding to the characteristic change owing to environmental fluctuation such as temperature. The ultrasound jelly generally used for inspection of the ultrasound system may be employed as the medium  95 , which allows the user to easily acquire the correction data. Furthermore, as the same jelly used for ultrasound irradiation as the one used in the diagnostic mode is employed for correction, the correction error may be reduced. 
         [0041]      FIG. 6  represents an example of a diagnostic flow for executing the ultrasound diagnosis to the living body in the ultrasound system according to the embodiment using the correction data stored in the calibration mode. The signs in parenthesis may be referred to  FIG. 6 , and other signs may be typically referred to  FIGS. 1 and 2 . Upon start (START) of diagnosis by the ultrasound system, the control circuit  50  sets various inspection parameters. The thus set parameters are used for gain correction carried out by the gain adjuster  44  with respect to the correction data acquired from the correction memory  46  of the above-described computation unit  45  in the calibration mode (S 30 ). 
         [0042]    The transmission waveform control unit  40  generates the first transmission reference signal waveform, based on which the first transmission signal is applied to the transducer elements  80 - 1  to  80 - n  via the transmission circuits  10 - 1  to  10 - n , respectively (S 20 ). The not shown living body is irradiated with transmission ultrasounds  200 - 1  to  200 - n  in accordance with the first transmission waveform via the medium  95 . Then reflection ultrasounds  210 - 1  to  210 - n  from the living body will be received (S 21 ). The transducer elements  80 - 1  to  80 - n  of the ultrasound oscillator array  90  detect (receive) the reflection ultrasounds  210 - 1  to  210 - n  in accordance with the first transmission waveform (S 22 ) so as to store the detection data in the reception data buffer  41 - 1  via the reception circuits  20 - 1  to  20 - n , and the ADCs  30 - 1  to  30 - n  (S 23 ). Similarly, the transmission waveform control unit  40  generates the second transmission reference signal waveform so that the second transmission signal is applied to the transducer elements  80 - 1  to  80 - n  via the transmission circuits  10 - 1  to  10 - n , and the detection data are stored in the data buffer  41 - 2  (S 24  to S 27 ). The first and the second transmission signals are those generated based on the PI method. The stored detection data  41   a ,  41   b  are added by the adder  42  (S 28 ). The addition result is subjected to the correction computation (S 29 ). The correction computation refers to the arithmetic operation based on the addition result in S 28  for subjecting the correction data computed for correction in S 30  to addition, subtraction, multiplication or division (S 29 ). 
         [0043]    This makes it possible to compensate for the positive-negative asymmetry with high accuracy in the signal transmission-reception system of the ultrasound system (main body) and the ultrasound array probe according to the embodiment. 
         [0044]    According to the operation flow shown in  FIG. 5 , if the correction data are acquired under the representative condition in the product shipment inspection performed by the manufacturer, the gain correction of the correction data by the gain adjuster  44  as shown in  FIG. 2  is automatically computed in the ultrasound system in accordance with the inspection parameters set by the user. Provision of a user adjustment panel as shown in  FIG. 8  allows the user to check as to application/non-application of the correction data, and perform fine adjustment of the correction value corresponding to the depth in the living body organ. This makes it possible to provide the ultrasound system with further excellent usability. 
         [0045]      FIG. 8  shows an exemplary structure of the user adjustment panel for the fine adjustment by the user. As the drawing clearly shows, the adjustment is enabled by checking a check box  61  on the user adjustment panel, which corresponds to the depth of the ultrasound reflection in the subject. Combinations of a scale  58  and a slider  59  are set corresponding to the respective depths, which allow the user to appropriately perform the fine adjustment of the predetermined correction degree in accordance with the depth in the living body. The user adjustment panel may be provided as hardware, or displayed on the display unit  60  as GUI (Graphical User Interface). The user of the ultrasound system is allowed to select the ultrasound image suitable for the diagnosis. 
         [0046]    The aforementioned structure allows acquisition of the correction data with high accuracy adapted to the user settings. As the user is allowed to carry out the correction while using the device, the highly accurate correction data may be acquired adapted to the characteristic change resulting from the environmental fluctuation such as temperature. In the case where the user has acquired the correction data, the ultrasound image determined by the user as being suitable for the diagnosis may be acquired by providing the measure for determining application/non-application of the correction value and adjustment. 
         [0047]    The ultrasound system according to the present invention allows correction of the positive-negative asymmetry in a series of systems employed for the general diagnosis from the transmission-oscillator (ultrasound transmission) to the oscillator-reception (reflected ultrasound detection). Therefore, the present invention provides the ultrasound system, and the ultrasound probe for realizing the high quality ultrasound image. 
         [0048]    The invention is not limited to the embodiments as described above, and may include various modifications. The embodiments have been described in detail for better understanding of the present invention, and are not necessarily restricted to the one provided with all the structures of the description. The structure of any one of the embodiments may be partially replaced with that of the other embodiment. Alternatively, it is possible to add the structure of any one of the embodiments to that of the other embodiment. It is also possible to have the part of the structure of the respective embodiments added to, removed from and replaced with the other structure. 
         [0049]    The aforementioned structures, functions and processing units have been explained by means of the operation flow as an example for producing the program which partially or entirely realizes them. It is also clear that they may be partially or entirely realized by hardware designed into the integrated circuit, for example. 
       REFERENCE SIGNS LIST 
       [0000]    
       
           10 ,  10   a - 10   n  transmission circuit 
           20 - 20   n  reception circuit 
           30   a - 30   n  analog to digital converter (ADC) 
           40  transmission waveform control unit 
           42  adder 
           43  correction computation unit 
           44  gain adjuster 
           45  computation unit 
           46 , 54  correction memory 
           47  fast Fourier transformer (FFT) 
           48  inverse FFT 
           49  interpolation computation/gain adjuster 
           50  control circuit 
           51 , 52  connector (CN) 
           53  connector box (BOX) 
           55  cable 
           56  ultrasound probe 
           57  sub-array 
           58  scale 
           59  slider 
           60  display unit 
           61  check box 
           70  user control unit 
           80  ultrasound transducer element 
           90  ultrasound transducer array elements 
           100 , 100   a - 100   n  transmission line 
           110 , 110   a - 110   n  reception line