System for reducing noise in an imaging catheter system
21 claims: 21 independent, 0 dependent
- 1カテーテルシステムにおいて、 遠位端及び近位端を 有する カテーテルと、 前記 カテーテルの遠位端の方に 位置した超音波 トランスデューサと、 前記 カテーテルの中に あり、かつ、前記超音波 トランスデューサに一端で接続 された伝送線とを備え、前記伝送線は、中央側導線と、前記中央側導線を囲うシールド体とを有しており、 さらに、前記伝送線の他端に接続されており、かつ、前記シールド体に生じる不要な電流を低減するためのチョークバランと、 前記チョークバランに接続された第1トランスと、 第2トランスと、 前記第1トランスと前記第2トランスとの間をつなぐスリップリングと、 を備えることを 特徴とする、カテーテルシステム。
- 2前記 伝送線が、同軸ケーブルを備えている、請求項1 に記載の カテーテルシステム。
- 3前記 チョークバランが、1以上のフェライト磁心と、 前記 1以上のフェライト磁心に巻かれた同軸ケーブル とを 備えている、請求項1 に記載の カテーテルシステム。
- 4前記 スリップリングが、水銀スリップリングを備えている、 請求項1に記載の カテーテルシステム。
- 5更に、 前記 第2トランスに 接続された 第2バランを備えている、 請求項1に記載の カテーテルシステム。
- 6更に、 前記 カテーテルの伝送線に 接続可能な 回転ハブを備えており、 前記 チョークバラン及び 前記 第1トランスが、 前記 回転ハブの中に収納されている、 請求項1に記載の カテーテルシステム。
- 7更に、 前記 回転ハブに回転可能に接続され、且つ、 前記 回転ハブを回転させるように 構成された モータ駆動ユニットを備えている、 請求項6に記載の カテーテルシステム。
- 8前記 第2トランスが、 前記 モータ駆動ユニットの中に収納されている、 請求項7に記載の カテーテルシステム。
- 9更に、 前記 カテーテルの遠位端の方に 位置した 位置センサと、 前記 カテーテルの中に あり、かつ、前記 位置センサに一端で 接続された 第2伝送線と、 前記 第2伝送線の他端に 接続された 第2チョークバランと、を備えている、請求項1 に記載の カテーテルシステム。
- 10前記 第2チョークバランが、フェライト磁心と、 前記 フェライト磁心に巻かれたシールド付き伝送線 とを備える、請求項9に記載の カテーテルシステム。
- 11前記超音波トランスデューサに接続された伝送線は第1伝送線であり、前記第2伝送線は、前記第1伝送線のシールド体に接続されたシールド体を含んでいる、請求項10に記載の カテーテルシステム。
- 12前記 第1伝送線が、同軸ケーブルを備えている、 請求項11に記載の カテーテルシステム。
- 13前記 シールド付き伝送線が、シールド付きツイストペア線を備えている、 請求項11に記載の カテーテルシステム。
- 14カテーテルシステムにおいて、 遠位端及び近位端を 有する カテーテルと、 前記 カテーテルの遠位端の方に 位置した超音波 トランスデューサと、 前記 カテーテルの中に あり、かつ、前記超音波 トランスデューサに一端で接続 された伝送線とを備え、前記伝送線は、中央側導線と、前記中央側導線を囲うシールド体とを有しており、 さらに、前記 伝送線の他端に 接続された第1トランスと、 第2トランスと、 前記 第1トランスと 前記 第2トランスとの間を つなぐ スリップリングと、 前記第2トランスに接続されたバランと、 を備えることを 特徴とする、カテーテルシステム。
- 15前記 伝送線が、同軸ケーブルを備えている、 請求項14に記載の カテーテルシステム。
- 16前記 スリップリングが、水銀スリップリングを備えている、 請求項14に記載の カテーテルシステム。
- 17前記 バランが、 前記 第2トランスからの平衡信号をシングルエンド信号に変換するように構成されている、 請求項14に記載の カテーテルシステム。
- 18更に、 前記 カテーテルの伝送線に接続可能な回転ハブを備えており、 前記 第1トランスが、 前記 回転ハブの中に収納されている、 請求項14に記載の カテーテルシステム。
- 19更に、 前記 回転ハブに回転可能に接続され、且つ、 前記 回転ハブを回転させるように 構成された モータ駆動ユニットを備えている、 請求項18に記載の カテーテルシステム。
- 20前記 第2トランスが、 前記 モータ駆動ユニットの中に収納されている、 請求項19に記載の カテーテルシステム。
- 21前記 第1トランスが、 前記 伝送線からのシングルエンド信号を平衡信号に変換するように構成されている、 請求項14に記載の カテーテルシステム。
Independent claims21
25 paragraphs, as filed
The technical field of the present invention is for medical imaging systems.<u style="single">Is related to</u>More specifically, to reduce noise in imaging catheter systems.<u style="single">Regarding the system.</u>
Treatment and diagnosis of pathological conditions, intraluminal, intraluminal, intravascular, and intracardiac, utilizing minimally invasive procedures, are effective tools in many areas of medical practice. These procedures are typically performed using imaging and therapeutic catheters. Imaging and treatment catheters are percutaneously inserted into the body and inserted into accessible blood vessels within the vasculature, away from blood vessels or organs for diagnosis and treatment, such as the femoral artery. To. The catheter is then advanced through the blood vessels of the vasculature towards the area within the body to be treated. The catheter may include an imaging device, typically an ultrasound imaging device. Imaging devices are used to find and diagnose diseased areas of the body, such as narrowed areas of arteries. For example, Patent Document 1 describes a catheter having an intravascular ultrasound imaging transducer (imaging transducer), which is patented by Harnm et al. And the disclosure of the patent is incorporated herein by reference.
FIG. 1 shows an example of an imaging transducer assembly (assembly unit) of a known technique. The imaging transducer 1 is typically within the lumen 60 of the guide wire (partially shown), the guide wire having a tubular outer wall member 5. The imaging transducer assembly 1 includes a coaxial cable 110, which comprises a central lead wire and an outer shielded wire (not shown). The conductor has a diameter of approximately 500 microns and is wound around the coaxial cable 110 to form a coil and function as the drive shaft 10. A stainless steel housing 20 is connected to the distal end (tip) of the drive shaft 10, which serves to reinforce the structure of the imaging transducer assembly 1. A conductive material, silver-epoxy resin 30, surrounds the coaxial cable 110 in the housing 20. Therefore, the housing 20 is electrically connected to the shielded wire of the coaxial cable 110 through the epoxy resin 30. At the distal end of the silver-epoxy resin 30, there is a non-conductive epoxy resin 35, which is an insulating material.
A layer of piezoelectric crystal (PZT) 80 is located at the distal end of the non-conductive epoxy resin 35 and is acoustically "sandwiched" between the conductive acoustic lens 70 and the conductive substrate 90. It is made of an absorbent material (eg, an epoxy substrate with tungsten particles). The acoustic lens 70 is electrically integrated with the central lead wire of the coaxial cable 110 through the connector 40. The connector 40 is insulated from the silver-epoxy resin 30 and the base material 90 by the non-conductive epoxy resin 35. The base material 90 is connected to the stainless steel housing 20. The imaging transducer assembly 1 is preferably surrounded by a sonolucent medium that allows the passage of ultrasonic waves without reflecting them back to the sound source. For this reason, the guide wire lumen 60 is also filled with saline around assembly 1. The drive shaft 10, housing 20, and acoustic lens 70 are exposed to saline solution. During operation, the PZT layer 80 is electrically excited by both the substrate 90 and the acoustic lens 70. The substrate 90 receives an electric charge from the shielded wire 140 of the coaxial cable 110 through the silver-epoxy resin 30, the stainless housing 20, and the acoustic lens 70. The acoustic lens may be silver-epoxy resin 30, but receives charge from the central lead 120 of the coaxial cable 110 through the connector 40. Similarly, the connector 40 may be silver-epoxy resin 30.
In some cases, it may be preferable to obtain information such as a three-dimensional longitudinal section of the same blood vessel as well as a cross-sectional image of the blood vessel. One approach to obtaining such additional information is to use medical positioning systems. The positioning system is a generally known technique. With reference to FIG. 2, a prior art positioning system 240 is shown. The system 240 generally comprises a plurality of transmitter and / or receiver nodes (connection points) 250, which can be arranged around the patient. For example, multiple nodes 250 can be placed on the skeleton of a tower that surrounds the patient. The system 240 further comprises one or more sensors 260. One or more sensors 260 are configured to transmit electromagnetic or electromechanical signals to or from node 250 of the transmitter and / or receiver. ..
The sensor 260 is integrated with the guide wire (partially shown), but can be placed in a blood vessel within the patient's body. The signal exchanged between the sensor 260 and the node 250 functions as a navigation signal. This signal can be used to determine the position of the sensor 260 within the patient's body, as will be apparent to those skilled in the art. In other words, the sensor 260 sends a navigation signal to the plurality of nodes 250, and the processor integrated with the node 250 (not shown) is based on the signals received by the plurality of nodes 250. Measure the position of. Alternatively, or in addition, the plurality of nodes 250 may transmit navigation signals to the sensor 260, and a processor integrated with the sensor 260 (not shown) may transmit signals transmitted by the plurality of nodes 250. The position of the sensor 260 in the patient's body may be measured based on. The medical positioning system 240 can track and record the position of the sensor 260 as it moves through the patient's blood vessels. Thus, the positioning system 240 provides a longitudinal section within the blood vessel.
As is known, the sensors of a medical positioning system can be coupled to an imaging transducer to form a transducer / sensor assembly 300. Referring to FIG. 2b, a side sectional view of an example of a transducer / sensor assembly 300 in a lumen 305 at the distal end of the assembly (partially shown) of a guidewire or catheter is shown. There is. The guide wire or catheter has a tubular outer wall 301. The transducer / sensor assembly 300 includes an imaging transducer 340 as described above and a sensor 320 for a medical positioning system. The "antenna" portion of the sensor 320 is an insulated lead wire 325. The lead wire 325 may have magnetism. The conductor 325 is tightly wound around the distal ends of the coaxial cable 410 and the non-conductive epoxy resin 330. The lead wire 325 is also tightly wound around the distal end of the drive shaft 310 to form a second coil. The second coil form preferably provides inductance for the antenna portion of the sensor 320 when charged to increase its ability to transmit or receive electromagnetic signals. A more detailed description of the catheter with the transducer / sensor composite assembly is provided in Patent Document 2, filed March 28, 2003, which is incorporated herein by reference in its entirety.<patcit num="1"><text>U.S. Pat. No. 5,368,035</text></patcit><patcit num="2"><text>U.S. Patent Application No. 10 / 410,901</text></patcit>
<p> The environment in which the imaging catheter generally operates includes other electronic devices, such as an electrocardiogram (EKG) system or other monitor. The electronic device is placed fairly close to the catheter so that the technician has convenient access to all devices. However, each of these devices produces an electromagnetic field, and if these devices are placed close enough, each electromagnetic field can cause signal distortion in the other device. Therefore, an improved imaging system is preferred.</p>
<p> The present invention provides a system and method for reducing noise in an imaging catheter system. In one embodiment, the catheter comprises an imaging transducer and a transmission line within the catheter to transmit a signal towards or from the transducer. A choke balun is connected to the proximal end (base-side end) of the transmission line to reduce noise generated by exposure of the transmission line to external interference. The choke balun allows a preferred transducer signal to pass through the transmission line while reducing noise introduced into the transmission line. In another embodiment, the transmission line consists of a coaxial cable with a central conductor surrounded by a shield. In this embodiment, the choke balun reduces the unwanted current induced in the shield of the coaxial cable by an external electric field from a nearby device.</p><p> In another embodiment, the signal from the rotating imaging transducer of the catheter is connected to the motor drive unit by a slip ring assembly. In this embodiment, the transducer signal is transformed into reduced noise from the slip ring assembly through first and second transformers located on either side of the slip ring assembly. The slip ring assembly preferably consists of a mercury slip ring.</p><p> In another embodiment, the balun is connected to a second transducer. This balun may be used to convert a balanced transducer signal to a single-ended signal and / or to reject in-phase noise to further improve the transducer signal.</p><p> In another embodiment, the catheter comprises a position sensor for tracking the position of the catheter. The position sensor is connected to a transmission line in the catheter to transmit a signal to the position sensor and to receive a signal from the position sensor. To further reduce noise, a second choke balun is connected to the proximal end of the second transmission line.</p><p> Other systems, methods, features and advantages of the present invention will be apparent or apparent to those skilled in the art with reference to the drawings and detailed description below. Of course, all such additional systems, methods, features and advantages are included in this description, are within the scope of the invention and are protected by the appended claims.</p>
With reference to FIG. 3, a schematic representation of a medical imaging system 1000 according to a preferred embodiment is shown. System 1000 includes an imaging catheter or guidewire 1020 as described above. The imaging catheter or guide wire 1020 is configured to be inserted into the lumen of the body and preferably into the vascular system within the body. The imaging catheter 1020 is detachably connected to the motor drive unit (MDU) 1010 through a hub 1040. The MDU1010 is electrically connected to the signal processing controller 1030. The MDU1010 includes a motor (not shown) connected to the drive shaft of the catheter 1020 to rotate the transducer. A more detailed description of the MDU is provided in US Pat. No. 6,261,246 filed September 28, 1998. U.S. Pat. No. 6,261,246 is incorporated herein by reference in its entirety.
As mentioned above, in a typical operating environment, other electronic devices are located near the imaging system 1000, and each of these magnetic fields may cause distortion in the signal lines of the imaging system 1000. One approach to address this issue is shown in Figure 4. FIG. 4 shows a diagram of a preferred circuit for hub 1040. In this embodiment, the hub 1040 is configured to be connected to an imaging catheter 1020, which comprises both a positioning sensor and an imaging transducer such as the transducer / sensor assembly 300 shown in FIG. 2b. There is. Hub 1040 connects the imaging catheter 1020 through a 9-pin interface 1100. As will be apparent to those of skill in the art, a catheter 1020 with a transducer / sensor assembly 300 generally comprises two different (not shown) transmission lines. The first transmission line is for the signal from the imaging transducer 340 and the second transmission line is for the signal from the position sensor 320. Generally, due to the nature of the data signal, such as the frequency range, the first and second transmission lines are of different types. The first transmission line is connected to the imaging transducer 340 and is a coaxial cable. The second transmission line is connected to the position sensor 320 and is a twisted pair line. Hub 1040 includes coaxial wire 1110 and shielded twisted pair wire 1120. Coaxial line 1110 is connected to a first transmission line for the imaging transducer 340. The twisted pair line 1120 is connected to a second transmission line for the position sensor 320.
The central conductor CC of coaxial line 1125 is connected to pin 8 of catheter interface 1100. The shield SHLD of coaxial 1125 is connected to pin 9 of catheter interface 1100. The coaxial line 1125 is wound around two juxtaposed ferrite cores J to form the first choke balun 1150. The first choke balun 1150 prevents the occurrence of signal distortion due to an electric field from another device or signal processing device 1030, as will be further described below. The central conductor CC and the shield SHLD of the coaxial line 1125 are further connected to the first printed circuit board PCB. The first printed circuit board PCB includes a third ferrite magnetic core J and a first wire BLUE and a second wire YEL wound around the third ferrite magnetic core J in order to form the first RF transformer 1160. The first wire BLUE is connected to the central conductor CC of the coaxial line 1125 and the shield body SHLD at both ends. The second wire YEL is connected to the central conductor and shield of the coaxial line 1100 at both ends. The hub circuit shown in FIG. 4 is rotated by the drive shaft of the MDU1010 along with the imaging transducer 340 and coaxial cable of the catheter.
Referring to FIG. 5, the transducer data signal in coaxial line 1110 goes through slip ring assembly 1130 to transducer line 1210 defined by a second printed circuit board (PCB) 1200 in MDU1010. The second printed circuit board 1200 includes circuit components for controlling the transmission and reception of data signals and for controlling the actual motor (not shown) in the MDU1010. An actual photograph of the second printed circuit board 1400 is shown in FIG. The slip ring assembly 1130 is electrically connected to a signal from the rotating circuit component of the hub 1040 to the circuit component 1200 of the MDU1010. To do so, the slip ring assembly 1130 comprises a conductor ring that is connected to the circuit components of hub 1040 and is located on an axis that rotates with hub 1040. The slip ring assembly also comprises a fixed conductor that is in electrical contact with the conductor ring and is connected to the circuit component 1200 of the MDU1010. An example of a slip ring assembly is given below with reference to Figure 9.
Slip ring assembly 1130 provides an interface between hub 1040 and MDU1010. The MDU1010 rotates the hub 1040 and the imaging transducer 340 in the catheter 1020. Traditional slip ring assemblies provide a mechanical connection between the hub and the rotary motor. However, mechanical connections generally introduce noise and high impedance circuits. Noise and high impedance circuits can generally cause problems for the transmission of ultrasonic and high frequency signals, as will be apparent to those skilled in the art. One solution is to include a mercury slip ring assembly 1130. Mercury slip ring assembly 1130 provides a pocket of conductive liquid mercury between the conductor ring and the fixed conductor. Thus, data transmission between conductors passes through liquid mercury. This results in a substantially lower impedance connection and lower noise than traditional mechanical connections. A photograph of the outer casing of the actual mercury slip ring assembly 1130 is shown in Figure 6. Another embodiment comprises a brush ring slip assembly, where a conductive bristle brush is utilized between the two conductors.
The second PCB1200 in the MDU1010 includes a second RF transformer 1220 connected to transmission line 1210. The 2nd RF Transformer 1220 has many features. For example, the second RF transformer 1220 electrically insulates the electrical signal of the catheter 1020 from the potential of the system 1000. This has resulted in the preferred "patient isolation" of the known technique. The second RF transformer 1220 is preferably placed on the area of glass fiber. The second PCB1200 may also include one or more baluns connected to the second RF transformer 1220 and the electronics of the MDU (not shown).
The operation of noise reduction circuit components for passing transducer signals will now be described with reference to FIG. FIG. 8 shows a simplified schematic of the noise reduction circuit components.
As described above, the signal from the imaging transducer 340 is sent to the catheter via the coaxial cable 410 consisting of the central lead wire CC and the shield body SHLD surrounding the central lead wire CC. The coaxial cable 410 is connected to the imaging transducer 340 at one end and to the noise reduction circuit component at the other end. The transducer signal in the coaxial cable 410 generates a current flowing in the central conductor CC and a current flowing in the shield body SHLD in the opposite direction with the same magnitude. Since the total current of the transducer signal is zero, the transducer signal can pass through the first choke balun 1150 with little or no attenuation. The coaxial cable shield SHLD also functions as an antenna that picks up external interference from nearby devices. The electric field from these devices creates an unwanted current on the outer surface of the shielded SHLD that causes signal distortion. The first choke balun 1150 provides high impedance for this unwanted shield current. Thereby, the first choke balun 1150 reduces unnecessary shield current and reduces the resulting signal distortion. The impedance seen near the unwanted shield current can be increased by increasing the number of turns on which the coaxial wire 1125 is wound around the ferrite magnetic core J, which forms the first choke balun 1150.
After passing through the first choke balun 1150, the transducer signal is converted to a balanced signal by the first RF transformer 1160. The balanced transducer signal consists of two opposite signals traveling on the separate lines 1210-1 and 1210-2 of the transmitting line 1210. The balanced transducer signal is connected to the second RF transformer 1220 by a pair of slip rings 1525 in slip ring assembly 1130. The balanced transducer signal facilitates the elimination of in-phase noise introduced into the signal by the slip ring assembly 1130, as described below.
The slip ring assembly can include an external casing 1550 and / or other parts that pick up external interference from nearby equipment. External interference may then be introduced into the balanced transducer signal by electrostatic coupling between the two slip rings 1525 and the outer casing 1550. The electrostatic coupling is visually demonstrated by the capacitor 1555 in FIG. Assuming that external interference affects both opposite balanced transducer signals equally, external interference is suppressed by the second RF transformer 1220. This is because the second RF transformer 1220 suppresses in-phase noise, that is, noise common to both opposite balanced signals. Thus, the first and second transformers 1160, 1220 located at both ends of the slip ring assembly 1130 operate to provide balanced transducer signals and suppress the noise introduced by the slip ring assembly 1130.
After passing through the second transformer 1220, the transducer signal can pass through another balun 1230. The balun 1230 can be used to convert the balanced signal into a single-ended signal for input to the MDU1010's electronics. FIG. 8 shows an example in which a single-ended signal is input to the MDU1010's amplifier for amplification and further processing. The balun 1230 can include one or more common mode rejection choke baluns, in order to improve the signal by further eliminating common mode signals.
Returning to FIG. 4, the noise reduction circuit component further comprises twisted pair wire 1120 connected to the twisted pair wire of the catheter. The twisted pair wire carries a signal toward the position sensor 320. Twisted pair wire line 1 BLUE and line 2 GRN are connected to pin 5 and pin 6 of the catheter interface, respectively. Twisted pair wire 1120 also shares a shielded body SHLD of coaxial wire 1110 to provide a shielded twisted pair wire. The shielded twisted pair wire is connected to the first PCB and is wound six times around the fourth ferrite core forming the second choke balun 1170 in the hub 1040. Like the first choke balun 1150, the second choke balun 1170 prevents signal distortion introduced into the twisted pair wire due to external interference from nearby electronics or signal processing equipment 1030. The second choke balun 1170 also suppresses the unnecessary shield current generated in the shielded body SHLD of the coaxial cable of the catheter and introduced into the shielded twisted pair wire. The shielded twisted pair wire 1120 is connected to the signal processor 1030 by a slip ring assembly 1130. Noise reduction circuit components for position sensors are not required for catheters that do not use position sensors.
FIG. 9 shows a schematic representation of an example of slip ring assembly 1130. The illustrated slip ring comprises four conductor rings 1610, 1620 on the axis 1630 of the MDU, and four fixed conductors 1615, 1625, respectively. Within the mercury slip ring assembly 1130, each conductor ring is electrically connected to the corresponding fixed conductor by liquid mercury. Two conductor rings 1610 are used to connect the transducer signal to the MDU1010, while the other two conductor rings 1620 are used to connect the position sensor signal to the MDU1010. The closeness of the conductor rings 1610, 1620 to each other may cause electrostatic coupling between the conductor rings. This electrostatic coupling is visually demonstrated by the capacitor 1635 in FIG. Transducer and position sensor signals generally operate in many different frequency ranges and therefore do not interfere with each other. However, the shielded twisted pair wire may transmit external interference within the frequency range of the transducer signal that can be introduced into the transducer signal by the electrostatic coupling 1635 between the conductor rings 1610, 1620. The second choke balun 1170 hinders the transmission of external interference by suppressing external interference. That is, the second choke balun 1170 generates a shielded current in the shielded twisted pair wire before external interference reaches the slip ring assembly 1130.
In the detailed description described above, the present invention has been described with reference to specific embodiments thereof. However, it is clear that various modifications and changes can be made here without leaving the broad spirit and scope of the present invention. For example, the reader is that the particular order or combination of process actions described herein is merely an example, and the present invention can be performed using different or additional process actions or different order or combination of process actions. Can be understood. For example, the present invention is particularly suitable for applications involving medical imaging devices, but can be used in almost any design including imaging devices. As a further example, each feature of one embodiment can be combined with other features shown in other embodiments. What's more, and obviously, features can be added or removed as desired. For example, the described embodiment includes a device that includes a transducer / sensor assembly 300 but only a transducer 340 (and corresponding circuit components), or a sensor 320 (and corresponding circuit components). A device comprising only) is always within the scope of the present invention. Accordingly, the present invention is not limited except by considering the appended claims and their equivalents.
In order to better understand the aforementioned and other advantages and objectives of the present invention, a more detailed description of the present invention briefly described above will refer to embodiments of the specification thereof. Will be given by. Embodiments are shown in the accompanying drawings. Of course, the contents of the drawings do not have to be on scale, but instead are emphasized in demonstrating the principles of the invention. Moreover, in the drawings, reference numerals and the like indicate the corresponding parts through different drawings. However, the parts and the like do not always have a reference code and the like. Moreover, all drawings are intended to convey the concept, and relative, size, shape, and other detailed properties are shown, either literally or exactly, rather than schematically. May have been.
<figref num="1a">It is a side sectional view of the imaging transducer of a known technique.</figref><figref num="2a">It is explanatory drawing of the medical positioning system of the prior art.</figref><figref num="2b">It is a side sectional view of the imaging transducer assembly of a known technique.</figref><figref num="3">It is a schematic diagram of a medical imaging system according to a preferred embodiment of the present invention.</figref><figref num="4">It is a schematic diagram of the circuit according to the preferred embodiment of the present invention.</figref><figref num="5">It is a schematic diagram of the circuit according to the preferred embodiment of the present invention.</figref><figref num="6">It is a photograph of a slip ring assembly according to a preferred embodiment of the present invention.</figref><figref num="7">It is a photograph of a printed circuit board according to a preferred embodiment of the present invention.</figref><figref num="8">It is a circuit diagram of the noise reduction circuit according to the preferable embodiment of this invention.</figref><figref num="9">It is a schematic diagram of an example of a slip ring assembly according to a preferred embodiment of the present invention.</figref>
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Numbers
- Publication
- 4979708
- Publication, DOCDB
- 4979708
- Publication, EPODOC
- JP4979708B
- Application
- 2008540380
- Application, DOCDB
- 2008540380
- Application, EPODOC
- JP20080540380
Titles2
- Japanese
- 撮像カテーテルシステムにおいてノイズを低減するためのシステム
- English
- A system for reducing noise in imaging catheter systems
Classification
- CPC, 4
- A61B8/12
- A61B5/06
- A61B2562/222
- A61B5/062
- IPC, 3
- A61B8 12
- A61M25 00
- A61M25 09
