WO2004073522A1 - 硬さ計測用カテーテルセンサ - Google Patents
硬さ計測用カテーテルセンサ Download PDFInfo
- Publication number
- WO2004073522A1 WO2004073522A1 PCT/JP2004/001740 JP2004001740W WO2004073522A1 WO 2004073522 A1 WO2004073522 A1 WO 2004073522A1 JP 2004001740 W JP2004001740 W JP 2004001740W WO 2004073522 A1 WO2004073522 A1 WO 2004073522A1
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- WO
- WIPO (PCT)
- Prior art keywords
- vibration
- catheter sensor
- catheter
- sensor
- hardness
- Prior art date
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Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
- A61B5/02007—Evaluating blood vessel condition, e.g. elasticity, compliance
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/12—Diagnosis using ultrasonic, sonic or infrasonic waves in body cavities or body tracts, e.g. by using catheters
Definitions
- the present invention relates to a catheter sensor for a thin tubular object, and more particularly, to a catheter sensor for measuring hardness for measuring a hardness of a measured portion such as an inner wall of a blood vessel.
- a hardness sensor for measuring hardness which uses a vibrator and measures hardness based on a change in the phase of radiation vibration and reflection vibration of the lever, is disclosed in There is a sensor disclosed in Japanese Patent No. 456991. Although it was possible to measure the hardness of the internal organs by inserting it into the body, the structure of the sensor part was complicated, and the sensor was so small that it could measure the hardness of the inner wall of blood vessels. It was not suitable for me.
- the conventional hardness sensor has a structure that is not suitable for miniaturization, so it is difficult to insert the sensor into a blood vessel and measure the hardness of lumps and clumps on the inner wall of the blood vessel and the like.
- the hardness sensor even when trying to apply a hardness sensor to a catheter as thin as 1 mm or less, it is difficult to miniaturize it if the structure of the vibrator etc. is complicated, and the hardness sensor is built in It was difficult to reduce the diameter of the catheter. Therefore, development of a fine sensor capable of measuring the hardness in a blood vessel has been desired.
- an object of the present invention is to provide a catheter sensor for measuring hardness in which a hardness sensor having a simple structure and advantageous for miniaturization is applied to a catheter. Disclosure of the invention
- a catheter sensor for hardness measurement includes a vibrating section that vibrates at a predetermined frequency and radiates vibration to a measured section; A receiving unit that receives the reflected vibration radiated from the measured unit and is radiated to the measured unit; a casing including the vibrating unit and the receiving unit; It comprises a signal processing unit for calculating the hardness of the part to be measured based on a change in the phase with the reflected vibration, and a liquid filled in the casing.
- the radiation vibration of the vibrating unit is transmitted to the measurement target via the liquid, and the reflected vibration from the measurement target is transmitted to the wave receiving unit via the liquid.
- the casing is provided with an inflatable balloon portion, and the balloon portion is inflated by increasing the liquid pressure of the liquid in the casing, comes into contact with the measurement target portion, and receives a signal from the vibration portion.
- the vibration may be such that the liquid is transmitted to reach the measured section via the balloon section.
- the vibrating part and the wave receiving part are provided at a part of the end of the catheter sensor opposite to the part to be measured, which is inserted into a blood vessel or the like, and is not inserted into the blood vessel or the like. Is also possible.
- the vibrating section is configured to emit vibration in the longitudinal direction of the catheter sensor, and further, the catheter sensor reflects the vibration from the vibrating section in a direction perpendicular to the longitudinal direction of the force table sensor. It has a reflection part, and the reflection part may be provided in the casing. Further, the reflecting section may be provided rotatably around the longitudinal direction of the catheter sensor.
- the vibrating section may be configured to emit vibration in a direction perpendicular to the longitudinal direction of the catheter sensor.
- the vibrating section may be rotatably provided around the longitudinal direction of the catheter sensor.
- the casing may be configured so as to be rotatable around the longitudinal direction of the catheter sensor.
- the vibrating unit and the wave receiving unit include one vibrator, and the one vibrator is provided with a ground terminal, an input terminal for the vibrating unit, and an output terminal for the wave receiving unit,
- the input terminal and the output terminal may be composed of split electrodes.
- the vibrating part and the wave receiving part are composed of two vibrators, one vibrator is provided with an input terminal and a ground terminal for the vibrating part, and the other vibrator is provided with a front vibrator.
- the output terminal and the ground terminal for the wave receiving unit may be provided.
- the vibrating part and the wave receiving part may be made of any one of a piezoelectric ceramic vibrator, a laminated piezoelectric ceramic vibrator, a piemorph vibrator, a crystal vibrator, a PVDF vibrator, a magnetostrictive element, and a SAW.
- the shape can be cylindrical, cylindrical, prismatic, or the like.
- the catheter sensor for hardness measurement of the present invention is advantageous in miniaturization because of its simple structure, and can be applied to a very fine catheter sensor. Therefore, it becomes possible to measure the hardness of the inner wall of a blood vessel in a minute blood vessel. In addition, since the measurement can be performed with directivity by rotating the reflection plate or the sensor itself for measurement, it is also possible to visually display hardness information in a blood vessel.
- FIG. 1 is a diagram for explaining an outline of a catheter sensor for measuring hardness according to the present invention.
- FIG. 2 is a diagram illustrating a configuration example of a signal processing unit of the catheter sensor for hardness measurement according to the present invention.
- FIG. 3 is a diagram for explaining the configuration of the sensor unit of the catheter sensor for measuring hardness according to the present invention.
- FIG. 4 is a diagram for explaining another configuration of the sensor section of the catheter sensor for measuring hardness according to the present invention.
- FIG. 5 illustrates another configuration of the sensor unit of the catheter sensor for measuring hardness according to the present invention.
- FIG. 6 is a diagram for explaining a state in which a reflecting plate provided in a sensor section of the catheter sensor for measuring hardness according to the present invention rotates.
- FIG. 7 is a diagram showing a display example of a measurement result when hardness in a blood vessel is measured by the directivity-based hardness measurement catheter sensor of the present invention.
- FIG. 8 is a diagram for explaining how the sensor section of the catheter sensor for measuring hardness according to the present invention rotates.
- FIG. 9 is a view for explaining a configuration in which the casing of the catheter sensor for measuring hardness according to the present invention rotates.
- FIG. 10 is a view for explaining a catheter sensor having a configuration in which the sensor portion of the hardness measuring force sensor according to the present invention and the portion reaching the portion to be measured are largely separated from each other, and the sensor portion is arranged outside the blood vessel. It is.
- FIG. 11 is a diagram for explaining the structure of a vibrator used in the hardness measuring force sensor according to the present invention.
- FIG. 12 is a diagram for explaining the shape of the vibrator used in the hardness measuring force sensor according to the present invention.
- FIG. 13 is a frequency-gain-phase characteristic curve diagram showing a total frequency characteristic obtained by synthesizing the respective frequency characteristics of the self-excited oscillation circuit and the phase shift circuit unit.
- FIG. 14 is a frequency-gain-phase characteristic curve diagram showing frequency characteristics of the self-excited oscillation circuit and the phase shift circuit unit.
- FIG. 1 is a schematic diagram of a catheter sensor for measuring hardness according to the present invention, and shows a state where a sensor unit 10 is inserted into a blood vessel.
- the sensor unit 10 inserted into the blood vessel radiates vibrations such as ultrasonic waves to the target part to be measured, such as a tumor, and receives the reflected vibration reflected from the target part by the sensor unit 10.
- the signal processing unit 20 measures the hardness of the part to be measured based on changes in the phases of the radiation vibration and the reflection vibration.
- the signal processing unit 20 is connected to the input of the sensor unit 10.
- a phase shift circuit section 21 and an amplifier circuit section 22 are provided between the outputs to form a self-excited oscillation circuit with forced feedback, and the output of the phase shift circuit section 21 is measured by the frequency measurement section 23.
- the signal processing unit calculates the hardness of the part to be measured by measuring the amount of change in the phase of the radiated vibration and the reflected vibration from the amount of change in the frequency. It is possible to apply the same one as the signal processing unit disclosed in Japanese Patent Publication No. 91 and International Publication No. WO 01 / 84135. The following describes the principle of measuring the phase change in the self-excited oscillation circuit. Fig.
- the frequency-gain characteristic curve TG is a total frequency characteristic obtained by combining the frequency characteristic of the self-excited oscillation circuit with the frequency characteristic of the phase shift circuit 21.
- the frequency-gain characteristic curve TG is low as shown in the figure. In the frequency band, the gain increases with increasing frequency, the gain becomes maximum in the band of the resonance frequency f., And the gain rises in the high frequency band.
- a resonance characteristic indicating a gain maximum value TGP of the frequency-gain characteristic curve TG is shown as an input / output phase difference which is a difference between an input phase and an output phase of the self-excited oscillation circuit.
- the input / output phase difference of the self-excited oscillation circuit is adjusted to zero at the frequency f. That is, in the self-excited oscillation circuit, the output phase () of the resonance frequency of the radiated vibration from the sensor unit 10 and the phase Shift circuit section 2 1 To an output is fed back to the sensor unit 1 0 input phase (e 2) a phase difference to be output combined phase difference theta 1!
- FIG. 14 is a frequency-gain-phase characteristic curve diagram showing frequency characteristics of the self-excited oscillation circuit including the sensor unit 10 and the signal processing unit 20 and the phase shift circuit unit 21.
- the horizontal axis is frequency
- the vertical axis is gain and phase, respectively.
- Phase shift As shown in the figure, the frequency-gain characteristic curve 13 G of the circuit section 21 shows that the gain increases with an increase in the frequency in the lower frequency band, the gain becomes maximum in the center frequency f 2 band, and the high frequency side In the band of, a curve with a peak that the gain decreases is drawn.
- a characteristic curve 0 13 is a phase characteristic showing an input / output phase difference of the phase shift circuit section 21.
- the characteristic curve MG is a frequency-gain characteristic curve of the self-excited oscillation circuit excluding the phase shift circuit section 21.
- the frequency-gain characteristic curve MG has a center frequency f and a different frequency band and a maximum gain value, but basically draws a peak curve like the frequency characteristic of the phase shift circuit 21.
- the center frequency fi of the self-excited oscillation circuit indicated by the gain maximum value P1 and the phase shift circuit section Set the center frequency f 2 indicated by the maximum gain value 1 3 GP of 2 1 to a frequency band that is intentionally shifted. For example, as the gain as the hardness factor of the measured portion it is high is high, to set the center frequency f 2 of the phase shift circuit 2 1 high frequency band with respect to the central frequency fi of the self-oscillating circuit.
- the frequency characteristic of the reflected vibration from the measured section received by the sensor section 10 changes according to the hardness of the measured section.
- the frequency, gain, phase, and amplitude of the self-excited oscillation circuit change. That is, the frequency of the self-excited oscillation circuit changes from the center frequency to the resonance frequency fu according to the hardness of the part to be measured. In the example shown in Figure 14, the frequency is increasing.
- the maximum value of the frequency-gain characteristic curve MG of the self-excited oscillation circuit changes from the maximum value Pi of the gain along the frequency-gain characteristic curve 13 G of the phase shift circuit section 21. That is, in the example shown in FIG.
- the frequency-gain characteristic curve MG of the self-excited oscillation circuit changes to M, the maximum gain value Pi to Pionat, and the gain to Gford.
- the phase shift circuit 21 adjusts the combined input / output phase difference ⁇ personallyto be zero, so that the frequency further changes until the feedback oscillation reaches a stable point where ⁇ ii becomes zero, and the gain Therefore, the frequency-gain characteristic curve MG 1 changes to MG 2 , the resonance frequency fii changes to f 2 , and therefore the maximum gain value P ii changes to P i 2 , and the gain G concernedchanges to G 1 2 Changes to Since the feedback loop of the self-excited oscillation circuit is a circuit that includes a resistance element and a capacitance element, the feedback loop between the input phase ⁇ and the output phase 0 2 The, there is always delta theta, the amount corresponding to the phase difference delta 6, the self-oscillation center frequency or to ⁇ the circuit, the gain until G 12, varies continuously.
- the frequency change amount f is obtained and the gain change amount AG is obtained.
- the input / output combined phase difference 0 ii becomes zero, and the self-excited oscillation circuit performs feedback oscillation.
- the frequency change amount ⁇ f at this time is taken out from the phase shift circuit section 21, and based on this, the hardness of the measured section can be measured.
- the frequency change A f is measured as a change that shifts to the positive side due to the stiffness effect
- the fluctuation amount A f is shifted to the negative side due to the mass effect.
- the shifting variable is measured.
- the phase difference of the reflected vibration with respect to the radiated vibration is different depending on the hardness of the object to be measured, so that the frequency change amount ⁇ f and the phase difference ⁇ 0 change according to the hardness. Can be expanded.
- the signal processing unit performs the frequency change, that is, the change in the phase between the radiated vibration of the vibrating unit and the reflected vibration of the wave receiving unit, based on the correlation between the hardness and the amount of change determined in advance. It measures the hardness of the part to be measured. Also, without using a feedback circuit, the input and output terminals of the sensor unit 10 are connected to a DSP (Digital Signal Processor) 25 as shown in Fig. The software may process the phase difference between the reflected vibration and the reflected vibration to form a feedback circuit so as to calculate the hardness of the measured part. As described above, the signal processing unit 20 performs any kind of signal processing based on the change in the phase of the radiation vibration and the reflection vibration, as long as the hardness of the measured part can be calculated. There may be.
- the resonance frequency f of the resonance circuit of the signal processing unit. lZ (2 ⁇ - ⁇ / LC) to detect the amount of change in L and C during measurement of the part to be measured, and calculate the hardness of the part to be measured based on this amount of change.
- lZ (2 ⁇ - ⁇ / LC)
- FIG. 3A shows only the sensor part of the catheter sensor for measuring hardness according to the present invention.
- the sensor unit 10 includes a vibrating unit 11 and a wave receiving unit 12 contained in a casing 13, and the casing 13 is filled with a liquid 14.
- Liquid 14 is a biopower
- a specific example is a physiological saline solution.
- the radiated vibration generated by the vibrating part 11 is radiated to the part to be measured via the liquid 14, and the reflected vibration reflected by the part to be measured is received by the receiving part 12 via the liquid 14. You.
- the radiation direction of the vibration of the sensor section 10 is configured to be directed to the longitudinal direction of the catheter sensor, and the rigidity of the measurement target section in front of the catheter sensor is measured. It has a structure that can measure the height.
- the vibration radiating section at the tip of the casing 13 has a structure that transmits the vibration and radiates it to the part to be measured, but the other parts of the casing 13 have a structure that reflects or absorbs the vibration. ing.
- an inflatable balloon portion 15 made of a thin film or the like may be provided in a part of the casing 13.
- the balloon section 15 is inflated as shown by increasing the liquid pressure of the liquid 14 in the casing 13, and the balloon section 15 comes into contact with the portion to be measured and is transmitted through the liquid 14. Is transmitted directly to the part to be measured.
- the balloon portion 15 is deflated, and after inserting the catheter sensor to the portion to be measured, the liquid pressure of the liquid 14 is increased during measurement to increase the balloon portion 1. 5 should be inflated and brought into contact with the part to be measured. With such a configuration, it is possible to more reliably radiate the vibration to the part to be measured.
- a reflector 16 may be provided as shown in FIG.
- the reflecting plate 16 is preferably provided at an angle of 45 degrees so as to reflect the vibration from the vibrating section 11 in a direction perpendicular to the longitudinal direction of the catheter sensor.
- the vibration from the vibrating part 11 travels through the liquid 14 to the reflector 16, is bent at a right angle by the reflector 16, is reflected, and passes through the vibration radiating part of the casing 13 to be measured. Is radiated.
- the reflected vibration from the part to be measured reaches the reflecting plate 16, is bent at a right angle, is reflected, is transmitted through the liquid 14, and is received by the receiving unit 12.
- the balloon 15 is provided as shown in FIG. 4 (b), and the balloon 15 is inflated by increasing the liquid pressure of the liquid 14 in the casing 13 as shown in FIG. 4 (b).
- the hardness can be measured by directly contacting the measured portion on the inner wall of the blood vessel in the direction perpendicular to the longitudinal direction of the catheter sensor.
- the radiation direction of the vibrating section 11 is directed in a direction perpendicular to the longitudinal direction of the catheter sensor, and to measure the hardness of the inner wall of the blood vessel and the like.
- the catheter sensor for hardness measurement configured as described above can measure the hardness of a part of the inner wall of the blood vessel in the blood vessel, but since the sensor has no directivity, it can be measured on the circumference of the inner wall of the blood vessel. It is impossible to measure the specific position, such as the force at which the tumor is located in the throat. Therefore, a structure of a catheter sensor capable of measuring the hardness at all portions on the circumference of the inner wall of a blood vessel by giving directivity to the measurement unit will be described below.
- FIG. 6 shows a configuration in which the reflection plate 16 of the catheter sensor of FIG. 4 is rotatable around the longitudinal direction of the catheter sensor.
- FIG. 6 (a) shows that the reflector 16 is positioned so as to radiate vibration downward in the drawing.
- vibrations are radiated to the far side in the drawing as shown in FIG. 6 (b).
- vibrations are radiated upward in the drawing.
- FIG. 6 (d) the vibration is radiated to the near side in the drawing, and when further rotated, it returns to the state of FIG. 6 (a).
- the reflecting plate 16 when the reflecting plate 16 is rotated around the longitudinal direction of the catheter sensor as an axis, it becomes possible to measure the hardness of all the blood vessel inner walls 360 degrees around the catheter sensor. As a result, the direction in which the vibration was emitted and the hardness of the inner wall of the blood vessel at that time can be measured, and the state of the hardness in the blood vessel is shown in Fig. 7 in combination with information on the catheter insertion amount (length, distance, etc.). As shown, it is possible to display three-dimensionally and in detail. For example, it is possible to make colors such as reddish as it gets harder and bluer as it gets softer, so it is possible to determine at a glance which part of a blood vessel has a tumor etc. Be able to do it visually.
- the force showing the casing 13 having the balloon portion 15 for measuring the hardness by bringing the sensor into contact with the inner wall of the blood vessel is not limited to this, and the present invention is not limited to this. It may be a casing that does not have an insect and measures hardness with a non-stripping insect.
- a catheter sensor configured such that the radiation direction of the vibrating section 11 as shown in FIG.
- FIG. 8 shows a catheter sensor that is configured to be able to measure the hardness of the entire circumference of the inner wall of a blood vessel by rotating about a shaft.
- FIG. 8 (a) shows the vibrating part 11 positioned in such a direction as to radiate vibration downward in the drawing. Then, by turning a wire or the like axially attached to the vibrating part 11, the vibrating part 11 rotates about the longitudinal direction of the catheter sensor as an axis, and as shown in FIG. Then, when it is further rotated, as shown in Fig. 8 (c), it radiates vibration upward in the drawing.
- a configuration may be adopted in which the casing 13 is rotated around the longitudinal direction of the catheter sensor while the vibrating section 11 is fixed.
- the inner surface of the cylindrical casing 13 is a reflection surface, and is configured so as not to transmit vibrations to the outside.
- the vibration part 11 is arrange
- a balloon portion 15 is provided in a part of the casing 13 so that the vibration is transmitted to the portion to be measured through the balloon portion 15.
- the balloon section 15 may be a simple thin film.
- FIG. 9 shows an example in which the vibrating part 11 is configured to vibrate radially
- the present invention is not limited to this, and the vibrating part is located on the side opposite to the part inserted into the blood vessel.
- a configuration in which the vibration of the vibrating portion is radially reflected in a direction perpendicular to the longitudinal direction of the catheter sensor by using a conical reflector or the like provided on the end side may be used.
- the catheter sensor for measuring hardness when applied to a catheter sensor for thinner blood vessels, for example, 0.5 mm or less, the diameter of the catheter becomes too small. In some cases, the sensor unit cannot be accommodated in the catheter. Even in such a case, in the catheter sensor for measuring hardness according to the present invention, since the casing 14 is filled with the liquid 14, as shown in FIG. In addition, it is possible to arbitrarily separate the position from the vibrator constituting the wave receiving unit. That is, the vibrating part and the wave receiving part are configured so as to be located at the end side of the catheter sensor opposite to the part to be measured inserted into the blood vessel or the like and not inserted into the blood vessel or the like. I do.
- the vibration of the vibrating part transmits the liquid 14 filled in the casing 13 and reaches the catheter tip.
- the vibration from the vibrator 11 transmits the liquid 14 to reach the reflector 16 and is reflected.
- the force is refracted by the plate 16 in the direction perpendicular to the longitudinal direction of the force sensor, and reaches the balloon portion 15 that has been inflated by increasing the fluid pressure.
- the reflected vibration reflected from the measured section is refracted by the reflector 16 again, transmitted through the liquid 14 and received by the wave receiving section 12.
- the vibrating part and the wave receiving part do not need to be inserted into a blood vessel or the like, but only need to be inserted with a catheter made of a casing filled with liquid. Therefore, the catheter sensor for measuring light hardness according to the present invention can make the diameter of the force catheter as thin as it can fill the casing with the liquid for transmitting vibration. It can be applied to ultra-fine catheters.
- FIG. 11 shows the structure of a vibrator used for the sensor section of the catheter sensor for measuring hardness according to the present invention.
- Figure 11 (a) shows an example in which a single oscillator is used.
- a thin film electrode is provided on the vibrator by vacuum deposition or the like.
- the vibrator 30 is provided with an input terminal 31 for a vibrating section, an output terminal 32 for a wave receiving section, and a ground terminal 33 as split electrodes.
- the vibrator 30 resonates and continues to vibrate at a stable frequency.
- the frequency output of the vibrator 30 can be taken out from the output terminal 32 for the receiving part.
- the reflected vibration reflected from the part to be measured hits the vibrator 30, a change appears in the frequency information obtained from the output terminal 32, and the amount of phase change between the radiated vibration and the reflected vibration at this time is measured. Used to measure the hardness of the part.
- the vibrator 30a is provided with an input terminal 31 and a ground terminal 33
- the vibrator 30b is provided with an output terminal 32 and a ground terminal 33. Even in this case, it is possible to extract the amount of phase change between the radiation vibration and the reflection vibration in the same manner as described above.
- the vibrator various elements such as a piezoelectric ceramic vibrator, a laminated piezoelectric ceramic vibrator, a bimorph vibrator, a crystal vibrator, a PVDF vibrator, a magnetostrictive element, and a SAW can be used.
- the shape of the vibrator can be cylindrical,
- various shapes such as a cylindrical shape and a prismatic shape, can be adopted according to the shape of the casing and the ease with which the ground terminal is provided.
- the catheter sensor for hardness measurement of the present invention is not limited to the above illustrated example, and it is needless to say that various changes can be made without departing from the gist of the present invention.
- the catheter sensor for measuring hardness of the present invention can be used not only for measuring hardness in blood vessels but also for measuring hardness in intestines and the like.
- the catheter sensor for measuring hardness of the present invention it is possible to obtain an excellent effect that the hardness of the inner wall can be measured even in a very minute portion such as a blood vessel.
Abstract
Description
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Priority Applications (2)
Application Number | Priority Date | Filing Date | Title |
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US10/546,415 US20070032727A1 (en) | 2003-02-20 | 2004-02-17 | Catheter sensor for measuring hardness |
EP04711741A EP1604613A4 (en) | 2003-02-20 | 2004-02-17 | CATHETER SENSOR FOR MEASURING HARDNESS |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
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JP2003042127A JP2004261233A (ja) | 2003-02-20 | 2003-02-20 | 硬さ計測用カテーテルセンサ |
JP2003-042127 | 2003-02-20 |
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WO2004073522A1 true WO2004073522A1 (ja) | 2004-09-02 |
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PCT/JP2004/001740 WO2004073522A1 (ja) | 2003-02-20 | 2004-02-17 | 硬さ計測用カテーテルセンサ |
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Country | Link |
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US (1) | US20070032727A1 (ja) |
EP (1) | EP1604613A4 (ja) |
JP (1) | JP2004261233A (ja) |
CN (1) | CN1774211A (ja) |
WO (1) | WO2004073522A1 (ja) |
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US9795442B2 (en) | 2008-11-11 | 2017-10-24 | Shifamed Holdings, Llc | Ablation catheters |
US8449466B2 (en) * | 2009-05-28 | 2013-05-28 | Edwards Lifesciences Corporation | System and method for locating medical devices in vivo using ultrasound Doppler mode |
CN102121120B (zh) * | 2010-01-11 | 2015-07-22 | 贵阳铝镁设计研究院有限公司 | 铝电解中的电解槽摇篮架 |
US9655677B2 (en) | 2010-05-12 | 2017-05-23 | Shifamed Holdings, Llc | Ablation catheters including a balloon and electrodes |
JP5792802B2 (ja) | 2010-05-12 | 2015-10-14 | シファメド・ホールディングス・エルエルシー | 低い外形の電極組立体 |
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US10349824B2 (en) | 2013-04-08 | 2019-07-16 | Apama Medical, Inc. | Tissue mapping and visualization systems |
CN110141177B (zh) | 2013-04-08 | 2021-11-23 | 阿帕玛医疗公司 | 消融导管 |
US10098694B2 (en) | 2013-04-08 | 2018-10-16 | Apama Medical, Inc. | Tissue ablation and monitoring thereof |
WO2017087549A1 (en) | 2015-11-16 | 2017-05-26 | Apama Medical, Inc. | Energy delivery devices |
WO2017110361A1 (ja) * | 2015-12-25 | 2017-06-29 | 古野電気株式会社 | 超音波解析装置、超音波解析方法、および超音波解析プログラム |
CN109925004A (zh) * | 2017-12-19 | 2019-06-25 | 苏州国科昂卓医疗科技有限公司 | 一种超声内窥探头和具有其的超声内窥导管及成像装置 |
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EP1016430B1 (en) * | 1997-09-12 | 2004-12-15 | Nippon Zeon Co., Ltd. | Balloon catheter |
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JP2001061793A (ja) * | 1999-08-27 | 2001-03-13 | Tokai Rika Co Ltd | 硬度センサ機構付きカテーテル及び硬度検出装置 |
CA2407511C (en) * | 2000-04-28 | 2010-04-13 | School Juridical Person Nihon University | Instrument for noncontact measurement of physical property |
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2003
- 2003-02-20 JP JP2003042127A patent/JP2004261233A/ja active Pending
-
2004
- 2004-02-17 EP EP04711741A patent/EP1604613A4/en not_active Withdrawn
- 2004-02-17 CN CNA2004800100659A patent/CN1774211A/zh active Pending
- 2004-02-17 WO PCT/JP2004/001740 patent/WO2004073522A1/ja not_active Application Discontinuation
- 2004-02-17 US US10/546,415 patent/US20070032727A1/en not_active Abandoned
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See also references of EP1604613A4 * |
Also Published As
Publication number | Publication date |
---|---|
US20070032727A1 (en) | 2007-02-08 |
EP1604613A1 (en) | 2005-12-14 |
EP1604613A4 (en) | 2006-08-16 |
JP2004261233A (ja) | 2004-09-24 |
CN1774211A (zh) | 2006-05-17 |
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