Apparatus for destroying a calculus

Abstract: An apparatus for destroying a calculus which is capable of setting a plurality of piezo-electric devices in drive/reception mode by phase control includes a peak value detecting unit (114) for detecting a peak value, in a predetermined time width, of an echo signal in a reception signal received by the piezio-electric devices, a first comparing unit (112) for comparing the peak value detected by the peak value detecting unit with a first predetermined threshold value, a frequency analyzing unit (113) for analyzing a frequency component, in the predetermined time width, of the echo signal in the reception signal, a calculating unit for calculating a predetermined characteristics value on the basis of frequency component data obtained by the frequency analyzing unit (113), a second comparing unit (114) for comparing the characteristic value obtained by the calculating unit with a second predetermined threshold value, and a display unit (116) for displaying a comparison result of the second comparing unit (114). The apparatus further comprises second control means (6) for controlling the acquiring means (3,4) so that morphological data having a low time resolution is acquired when the shock wave is not radiated and a high time resolution when the shock wave is radiated. The apparatus further comprises calculating means and display means for changes over time in destruction voltage, destruction rate and treament mode.

Description: The present invention relates to a shock wave calculus destroying apparatus and, more particularly, to an apparatus for destroying a calculus which uses an ultrasonic imaging unit to position a calculus and confirm the destruction state of the calculus. Recently, in treatment of a renal calculus or a gallstone, a method of non-invasive treatment using a shock wave is popularly used. Typical examples of a shock wave generating source include underwater discharge, electromagnetic induction, and a piezo-electric device, which have individual features. Various methods are used for positioning a calculus at a focal point of a shock wave and for confirming the destruction state of the calculus. Especially, a method of generating a shock wave by using a piezo-electric device has an excellent feature. More specifically, no consumable is used, the intensity of the shock wave can be arbitrarily controlled, and the focal point can be controlled by controlling the phase of the drive pulse applied to a plurality of piezo-electric devices (e.g., Published Unexamined Japanese Patent Application No. 60-145131 and U.S.P. No. 4,526,168). In the initial stage of development of an apparatus for destroying a calculus, positioning and confirmation of the destruction state were performed by using X-ray TVs in two directions (e.g., Published Unexamined Japanese Patent Application No. 62-94144). With this method, however, the patient and the operator can be exposed to X-ray radiation, and continuous monitoring cannot be performed in order to minimize the X-ray dose as much as possible. In contrast to this, in order to perform positioning and destruction state confirmation, recently, a method using an ultrasonic imaging unit is often employed (e.g., Published Unexamined Japanese Patent Application No. 60-145131). According to this method, a location to install an ultrasonic probe is limited to the inside or outside of a shock wave generating source. Nevertheless, this system receives a great deal of attention as it does not cause X-ray exposure and it can perform continuous monitoring. In particular, since the ultrasonic imaging unit is a semi-real-time image diagnosing unit, it can continuously monitor the state of a calculus. Since continuous monitoring is possible, even if the position of the calculus is deviated from the focal point of a shock wave due to a respiratory movement or the body movement of the patient, positional deviation can be immediately confirmed, and radiation of the shock wave is stopped in such a case. When the ultrasonic imaging unit is used in the medical application described above, it is especially significant to detect a small calculus of about 5 mm. For this purpose, in order to improve the resolution, a so-called multi-stage focus is used, or the number of scanning lines per frame is increased. In this case, a high-resolution image can be obtained over a wide range by decreasing the frame rate (repetition frequency of the ultrasonic image = frame count per second) of the ultrasonic imaging unit. The real-time characteristics of the ultrasonic imaging unit are sacrificed more or less. Use of an apparatus for destroying a calculus having such an ultrasonic imaging unit in an actual clinical case will be described. A high-resolution image is required before detection of a calculus is started in order to obtain the position of the calculus on a screen displaying an ultrasonic image. Once treatment is started, the frame rate can be increased. This policy is applicable without any problem when a slow movement of a calculus such as a respiratory movement is to be monitored. However, if the high resolution of an image is achieved simply by decreasing the frame rate, the following problems arise. These problems will be described below. The present inventors conducted the following experiment. In this experiment, a shock wave was radiated on a calculus placed in water to destroy the calculus. According to this experiment, when destruction of the calculus proceeded by shock wave radiation and small calculus fragments were started to be formed, the fragments were observed to jump in synchronism with shock wave radiation. This phenomenon is called a stone dance. A similar phenomenon was observed in destruction of a calculus in a human body. Accordingly, this stone dance can serve as effective information indicating the calculus destruction state. Since the stone dance, however, is a quick phenomenon, it was difficult to observe it on an ultrasonic image at a low frame rate. In the apparatus for destroying a calculus of this type, a single radiation shock wave operation is insufficient in most cases and repetitive radiation over a multiple of times is usually performed. A radiation count until calculus destruction is completed varies depending on the type of the calculus, the figure of the patient, the depth of the location of the calculus from the body surface, the energy of the shock wave, and the like. Hence, to record and reserve a numerous treatment data is effective in appropriately setting the shock wave radiation count. It is indispensable in terms of improvement of the treatment efficiency and safety to grasp the treatment state as a treatment trend during treatment. Regarding the treatment method, an erroneous radiation preventive treatment mode for radiating a shock wave once or continuously without damaging tissues around the calculus has started to be employed. An erroneous radiation preventive treatment mode is described in Published Unexamined Japanese Patent Application Nos. 60-191250, 61-149562, and so on. The erroneous radiation preventive treatment mode is as follows. That is, when a piezo-electric device is used as a shock wave source, a fact that a wave reflected by the focal region of the shock wave can be received by the piezo-electric device is utilized. A weak ultrasonic wave is transmitted and received by the piezoelectric device immediately before an intense shock wave is emitted. When an intense echo is received, it is determined that the focal region of the shock wave coincides with the calculus. When this determination is made, a shock wave is irradiated on the calculus. This erroneous radiation preventive treatment mode cannot be applied to all patients, as an intense wave is not always reflected by the patient. If an intense wave is not reflected by the patient, first, shock waves are continuously radiated in accordance with the treatment mode. Along with the procedure of destruction, when an intense wave is started to be reflected by the patient, the erroneous radiation preventive treatment mode may be set in place of the treatment mode. In an apparatus for destroying a calculus having a shock wave source using underwater discharge or a small explosion, a mode having a similar function to the erroneous radiation preventive treatment mode is provided in addition to the treatment mode for radiating the shock wave once or continuously. According to this mode, a shock wave is radiated only during the inspiration end period of the respiration so as not to damage the tissues around the calculus, or a shock wave is radiated in synchronism with the electrocardiogram. When this mode is set, a destruction treatment mode is sometimes changed to another destruction treatment mode during a single destruction treatment. Regarding the destruction rate, the higher the destruction rate, the faster the treatment is completed naturally. When the destruction rate is increased, however, the patient feels pain, or the destruction pressure is decreased due to cavitation. Therefore, the rate must be changed to an optimum value on the basis of the judgement of the doctor. In this manner, not only the destruction energy quantity (more particularly, the drive voltage of the shock wave source, e.g., the piezo-electric device, and the pressure of the shock wave) but also the destruction treatment mode and the destruction rate serve as significant factors in terms of the treatment efficiency and safety. However, the treatment trend of the conventional apparatus for destroying a calculus includes only the transition graph (the radiation count is plotted along the axis of abscissa) of the destruction energy and the patient data (e.g., name, age, patient's ID No., and name of the disease) which are insufficient to evaluate the treatment efficiency and grasp the safety. According to the erroneous radiation preventive treatment mode described above, only an ultrasonic image or an X-ray image can be used to determine the destruction degree of a calculus, and such a determination is not so reliable. Thus, even if the apparatus has a function of radiating the shock wave only to the calculus, the shock wave can be radiated continuously even after destruction is completed. In this case, damage to the normal tissues around the calculus cannot be neglected, and the treatment time becomes longer than necessary. Inversely, if the dose of the shock wave is excessively small, another treatment section will be need, and impaction of a large calculus fragment in an ureter may occur. DE-U-3617032 discloses an apparatus for destroying a calculus corresponding to the preamble of claim 1 It is an object of the present invention to provide an apparatus for destroying a calculus which can position a shock wave source easily and which can monitor a destruction state properly. It is another object of the present invention to provide an apparatus for destroying a calculus which can evaluate a treatment efficiency properly and which can display a treatment trend for confirming the safety. It is still another object of the present invention to provide an apparatus for destroying a calculus which can properly radiate a shock wave only on a non-destroyed calculus, which minimizes a side-effect, and which has a high treatment efficiency. The above objects are achieved by an apparatus as defined in Claim 1. This invention can be more fully understood from the following detailed description of an embodiment, by way of example only, when taken in conjunction with the accompanying drawings, in which: Fig. 1 is a schematic diagram showing an arrangement of an apparatus for destroying a calculus according to an embodiment of the present invention; Fig. 2 shows an arrangement of an ultrasonic imaging probe and an ultrasonic imaging unit in detail; and Figs. 3A and 3B are views for explaining frame rate control by selection of the number of steps of a multi-stage focus of the embodiment of Figures 1 and 2. The preferred embodiment of the present invention will be described with reference to the accompanying drawings. Fig. 1 shows an arrangement of an apparatus for destroying a calculus. A shock wave source 1 has, as major components, a spherical member (not shown) and a plurality of piezo-electric devices arranged on the inner surface of the spherical member to constitute a sperhical shell. The shock wave source 1 is supported by a known support unit (not shown) and can be manually moved. The shock wave source 1 can also be moved by a known mechanism (not shown) using an electric power, an electro-magnetic force, or a fluid pressure. The shock wave source 1 is moved mainly to cause the focal point of the shock wave to coincide with the calculus. The shock wave source 1 is driven by a high-voltage pulse supplied from a pulser 8 to generate a shock wave. The shock wave is focused on a focal point F as the geometric center of the spherical shell. A region near the focal point F is referred to as a focal region. An ultrasonic imaging probe 3 for drawing and positioning a calculus 2 is provided inside the shock wave source 1. The probe 3 is arranged at the center of the interior of the shock wave source 1. The probe 3 can slide back and forth and can rotate and is arranged in an ultrasonic imaging unit 4. A typical example of the ultrasonic imaging unit 4 is an ultrasonic imaging unit SSA-270A manufactured by TOSHIBA CORPORATION. When an ultrasonic wave is transmitted to and received from a living body (not shown) by the probe 3, an ultrasonic image on a slice including the focal point F is drawn. In this embodiment, an electronic sector scanning probe is used as the probe 3. The ultrasonic imaging unit 4 can increase or decrease the number of focal points of the electronic focus during ultrasonic transmission or reception or both. More particularly, the ultrasonic imaging unit 4 can employ 4-stage focus in ultrasonic transmission. When 4-stage focus is performed, a high-resolution ultrasonic tomographic image can be obtained over the entire area of the screen. A position detector 5 measures the relative positions (distance) of the shock wave source 1 and the probe 3. For example, a potentiometer is used as the position detector 5. The potentiometer is arranged in the shock wave source 1 so as to be cooperated with the forward and backward movements of the probe 3. The position detector 5 outputs position data of the probe 3 in the form of an electrical signal. The output signal from the position detector 5 is supplied to the ultrasonic imaging unit 4 through a system controller 6. The ultrasonic imaging unit 4 superimposes a marker indicating the position of the focal point F on the basis of the signal from the position detector 5. Fig. 2 shows an arrangement of the ultrasonic imaging probe 3 and the ultrasonic imaging unit 4. The probe 3 has a plurality of ultrasonic transducers arranged therein. The ultrasonic wave can be deflected and electronically focused by phase-controlling each transducer 11 during ultrasonic transmission or reception or both. Each transducer 11 is connected to a transmission circuit 12 and a reception circuit 13. Each transmission circuit 12 receives a trigger pulse from the system controller 6 through a transmission delay circuit 14 to pulse-drive the corresponding transducer 11. The ultrasonic pulse emitted from the transducer 11 is radiated on the interior of the patient's body and reflected by a reflecting member, e.g., a calculus. The respective echoes are received by the transducers 11, amplified by the reception circuits 13, and supplied to an adder circuit 16 through reception delay circuits 15 to be added with each other. An output signal from the adder circuit 16 is detected by a detection circuit 17 and input to a DSC (Digital Scan Converter) 18 comprising an A/D converter, a digital image memory, a D/A converter, and the like. Image data obtained by the DSC 18 is supplied to a CRT display 19, and a B-mode tomographic image of the patient's body is displayed on the display 19 as an ultrasonic image. The delay times of the transmission and reception delay circuits 14 and 15 are controlled by the system controller 6. That is, the respective ultrasonic transducers 11 are controlled by the corresponding transmission circuits 12 with relative delay time differences. During reception, the echo signals output from the reception circuits 13 are supplied to the adder circuit 16 with the same delay time differences as those in transmission, thereby focusing the ultrasonic beam. This focusing function of the ultrasonic beam by way of control of the delay time is called electronic focus. Control of the delay time described above realizes phase control. In this case, a change in focal point of the electronic focus and formation of a plurality of focal points in one frame image are realized by controlling the delay time of at least either the transmission delay circuits 14 or the reception delay circuits 15 and by controlling an increase or decrease in number of transducers used for driving. This operation is known well as multi-stage focus or dynamic focus. In this embodiment, the frame rate is increased when the shock wave is radiated and decreased when the shock wave is not radiated by the system controller 6 by changing the number of stages of the multi-stage focus, i.e. by changing the number of focal points. It suffices if multi-stage focus is employed only during transmission. Figs. 3A and 3B schematically show frame rate control. In this example, the number of stages of multi-stage focus is 4 at maximum, as shown in Fig. 3A, and four focal points f1 to f4 are formed. Fig. 3B shows a state in which the number of focal points is decreased to 2, i.e., the focal points f2 and f3. In actual treatment, the operator moves the shock wave source 1 to cause the focal point F to coincide with the calculus 2 while he observes the ultrasonic screen. Movement of the shock wave source 1 is realized manually or non-manually, as described above. When the shock wave source 1 is to be moved non-manually, electricity, electromagnetic energy, or a fluid pressure is employed. During positioning, the system controller 6 controls the ultrasonic imaging unit 4 to be set in the multi-stage focus mode, i.e., such that the four focal points f1 to f4 are formed, as shown in Fig. 3A. When positioning is completed, the operator depresses a treatment start/end switch 7 provided to the system controller 6 to instruct radiation start of the shock wave. The system controller 6 supplies a trigger to the pulser 8 in response to this instruction, and the pulser 8 drives the piezo-electric device group of the shock wave source 1 with a high voltage. At this time, the system controller 6 supplies treatment start data to the ultrasonic imaging unit 4 simultaneously. Then, the system controller 6 controls the ultrasonic imaging unit 4 until treatment is stopped such that its focal points are formed only in the vicinity of the focal point F of the shock wave source 1, e.g., only at two portions before and after the focal point F as the focal points f2 and f3, as shown in Fig. 3B. As a result, the frame rate of the ultrasonic imaging unit 4 becomes twice that during multi-stage focus. When the probe 3 is moved back and forth during treatment, it is apparent that the positions of the focal points of the ultrasonic imaging unit 4 must be changed in accordance with the depth of the moved focal point F. When the treatment is completed with the calculus being destroyed, or when the calculus is moved and repositioning is needed, the treatment start/end switch 7 is depressed again to stop the treatment. At this time, treatment stop data is supplied from the system controller 6 to the ultrasonic imaging unit 4 and the pulser 8, in a reverse order to the operation described above, to stop driving of the shock wave source 1, and the initial multi-stage focus, i.e., the state shown in Fig. 3A is restored. In this embodiment, the number of stages of variable focus is decreased in order to increase the frame rate. However, since scanning of the ultrasonic imaging unit 4 used for positioning of an apparatus for destroying a calculus of this type is generally of an electronic sector type, the same effect can be obtained even if the sector scanning angle of the ultrasonic image is decreased. The technique to change the sector scanning angle in a sector scanning-type ultrasonic imaging unit is known to a person skilled in the art. Accordingly, even if the condition of multi-stage focus is unchanged after the treatment is started, if the sector angle is decreased to half, the frame rate can be increased twice. Note that when the sector scanning angle is to be decreased during shock wave radiation, the sector scanning angle must be set such that the scanning range covers at least the focal region of the shock wave. In this embodiment, a shock wave source using piezo-electric devices is employed. However, the present invention can similarly be applied to an underwater discharge or electromagnetic induction type shock wave source. In this embodiment, an electronic sector scanning-type ultrasonic imaging unit is employed. However, an ultrasonic imaging unit, e.g., a mechanical sector type ultrasonic imaging unit using annular array vibrators whose frame rate is decreased when the resolution is increased in multi-stage focus can be used. In this embodiment, the ultrasonic imaging probe 3 is arranged inside the shock wave source 1. However, it can be arranged outside the shock wave source 1. In this embodiment, a CRT is used as a means for conveying data to the operator. However, e.g., the intensity of the echo can be expressed by the intensity of a sound, and the degree of destruction can be expressed by a timbre. Also, audio representation and visual representation by the CRT can be combined.

Claims: An apparatus for destroying a calculus, comprising: shock wave radiating means (1) for radiating a shock wave to a calculus in a living body, first control means (8) for controlling radiation of the shock wave, and acquiring means (3, 4) for acquiring morphological data from the living body, characterized by further comprising: second control means (6), for cooperation with said shock wave radiating means (1) and for controlling said acquiring means such that the morphological data are acquired at a relatively large frame rate when the shock wave is being radiated under the control of said first control means (8), and the morphological data are acquired at a relatively small frame rate when the shock wave is not being radiated. An apparatus according to Claim 1, in which said acquiring means (3, 4) is an ultrasonic tomographic imaging unit comprising: ultrasonic tomographic image acquiring means (11, 12, 13, 14, 15, 16, 17) for acquiring an ultrasonic tomographic image in units of frames as the tomographic image at a predetermined frame rate, and means (18, 19) for displaying the ultrasonic tomographic image acquired by said ultrasonic tomographic image acquiring means (11, 12, 13, 14, 15, 16, 17). An apparatus according to Claim 2, in which the frame rate is determined in cooperation with said first control means (8). An apparatus according to Claim 2 or 3, in which the ultrasonic tomographic image acquiring means is controlled by the second control means (6) to form an ultrasonic tomographic image using at least one focus, when the shock wave is not being radiated. An apparatus according to Claim 2 or 3, in which the ultrasonic tomographic image acquiring means is controlled by the second control means (6) to increase or decrease the number of stages of a multi-stage focus to determine respectively the relatively small or the relatively large frame rate.

Inventors: AIDA SATOSHI C O INTELLECTUAL, FUJIMOTO KATSUHIKO C O INTELLE, ISHIDA AKINORI C O INTELLECTUA, IWAMA NOBUYUKI C O INTELLECTUA, SUZUKI KAORU C O INTELLECTUAL, AIDA, SATOSHI, C/O INTELLECTUAL PROPERTY DIV., FUJIMOTO, KATSUHIKO, C/O INTELLECTUAL PROPERTY DIV, ISHIDA, AKINORI, C/O INTELLECTUAL PROPERTY DIV., IWAMA, NOBUYUKI, C/O INTELLECTUAL PROPERTY DIV., SUZUKI, KAORU, C/O INTELLECTUAL PROPERTY DIV.
Applicants: TOSHIBA KK, KABUSHIKI KAISHA TOSHIBA
Application year: 1992
Main classification: A61B17
IPC codes: A61B17, G01S15