CN101983077B - 新型医疗搏动装置 - Google Patents
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Abstract
本发明涉及一种新型搏动医疗装置,其包括:导管(1),所述导管(1)设计成***血管中,具有直径,并在其称为A部的***端处具有杆;可膨胀部件(6),所述可膨胀部件(6)被容纳在所述导管(1)称为B部的部分的周围,所述可膨胀部件(6)设计成连接至充胀装置(9),该充胀装置(9)连接于所述导管(1)称为C部的另一端,从而使所述可膨胀部件能够以脉冲的方式膨胀/收缩,所述导管(1)的B部直径小于所述导管(1)的A部和C部的直径,而所述导管(1)的A部和C部的直径近似相等。
Description
技术领域
本发明涉及一种新型搏动医疗装置。
背景技术
从概念上讲,心血管***是一种内部排列有上皮细胞的加压封闭液压回路。这些上皮细胞的功能由心脏搏动调节,心脏搏动引起血管内的压力变化,并进而这些细胞的剪切力,并刺激这些细胞。在氧化氮合成(NOS)、血液凝固、炎症反应、免疫性、动脉粥样硬化、血管再生和细胞凋亡时,这些切向剪应力对于维持包括血管张力在内的内皮功能是必要的。内皮功能非常重要,因为其控制胚胎发育、形态发生、器官形成以及健康身体的维持。
在此回路上的诸如疾病或外科手术的任何干预都会引发具有潜在的显著后果的内皮功能紊乱。
如今,在循环辅助领域中使用了许多搏动装置。在这些搏动装置中,主动脉内球囊反搏(IABP)由于其易用性及廉价性而使用最为广泛。
专利申请US 2001/0031907公开了一种搏动血液循环辅助装置,其包括:
-导管,所述导管***血管中,并且具有直径,而且在其***端处具有杆,以及,
-可膨胀部件,所述可膨胀部件被容纳在导管的部分的周围,并在膨胀时增加冠状动脉的(心脏)舒张压,所述可膨胀部件设计成连接至设置于所述导管另一端的充胀装置,从而使所述可膨胀部件能够以脉冲方式膨胀/收缩。
目前,在需要将上述类型的具有可膨胀部件或膨胀囊的导管***患者的血管中时,使用了由导向管和止回止血阀组成的***装置。导向管的***产生一开口,该开口具有足够直径以使随后***所述导向管中的膨胀囊导管,而设置在***点处的所述阀能够减少并阻止血液流动通过***装置。
根据现有技术的膨胀囊导管的缺点在于,如果需要将所述膨胀囊导管不通过***装置而是直接***血管——例如在需要将膨胀囊导管留在适当位置一定时间,或对于小直径导管(即在几个毫米或更小的范围)的情况下,就不能忽视血流的风险。确实,在直接***膨胀囊导管的过程中,起初等于导管直径的***点直径在导管的被膨胀囊包绕的部分通过后扩大了。随后,在将导管***得更深以将膨胀囊定位在待治疗的区域时,导管直径小于***点直径,因此就会有血流的风险。
发明内容
因此,本发明通过一种搏动医疗装置解决此问题,其包括:
-导管,所述导管将被***血管中,具有直径,并在称为A部的***端处具有杆,以及
-可膨胀部件,所述可膨胀部件被容纳在所述导管的被称为B部的部分的周围,所述可膨胀部件设计成连接至设置在被称为C部的所述导管另一端的充胀装置,从而使所述可膨胀部件以脉冲的方式膨胀/收缩,
其特征在于,所述导管的B部直径小于所述导管的A部和C部的直径,并且,所述导管的A部和C部的直径基本相等。
导管的B部直径的所述减小使得导管整个B部加上可膨胀部件的直径能够相对于根据现有技术的导管的直径减小。将导管***患者血管中后,将不会发生由于导管的部分的明显较大的直径而造成所述***点的过度扩张。
在本发明一种特别的实施方式中,导管B部加上收缩的可膨胀部件的直径小于或等于导管A部和C部的直径。在此实施方式中,导管的***不会引起***点的任何扩张,这更为有利。
在一种特别的实施方式中,可膨胀部件是膨胀囊。
优选地,可膨胀部件由生物适应性的辐射透不过的材料制成。因此,将所述可膨胀部件***血管不会引起任何感染或其他损害,并可以通过放射照相术很容易地观察到。
在一种特别的实施方式中,所述材料是聚氨酯;此材料是有利的有机材料中的一种示例。
在本发明的一种特别的实施方式中,所述导管的直径为几毫米或更少。这些尺寸对应于在儿科中使用的以及对成人使用以便到达某些细小血管的小型导管。但是,本发明要解决的问题——该问题为当需要在不具有导向管情况下使用膨胀囊导管时改变所述膨胀囊导管的直径,在使用小直径导管的情况下显著增加了。确实,对于这些小型导管而言,膨胀囊的厚度和直径较大的导管的膨胀囊厚度相比在直径上的增加在比例上明显较大。
在本发明的一种特别的实施方式中,可膨胀部件的尺寸为长度在0.1cm至2cm之间,体积在0.1cm3至2cm3之间。
本发明还涉及一种搏动医疗组件,其包括上述搏动装置以及充胀装置,所述充胀装置包括:
-囊袋,所述囊袋适于被填充流体,
-囊袋压缩装置,所述囊袋压缩装置适于以脉冲方式压缩所述囊袋;以及
-连接装置,所述连接装置将所述囊袋连接至所述导管的可膨胀部件,使得所述流体能够在所述可膨胀部件与所述囊袋之间循环。
此搏动医疗组件易用且廉价。此外,由于其尺寸紧凑,所以便于携带。所述囊袋压缩装置可以手动操作并通过用板以平移或旋转的方式、或使其中一板向另一保持静止的板平移的方式来压缩囊袋而实施,或由将囊袋容纳其中的室来实施。
在搏动医疗组件的一种特别的实施方式中,所述囊袋压缩装置以电动机械的方式被控制。
在搏动医疗组件的一种特别的实施方式中,搏动装置与充胀装置是一体的。
附图说明
现在参照附图描述本发明的一种实施方式:
图1表示根据本发明的搏动装置在膨胀囊收缩时的纵剖面;
图2表示根据本发明的搏动装置在膨胀囊膨胀时的纵剖面;
图3表示连接于充胀装置的一种特别的实施方式的根据本发明的搏动装置的纵剖面。
具体实施方式
图1、图2和图3中示出的根据本发明的搏动装置由导管1组成,所述导管1是中空管,其具有三个相继的部分A、B和C。A部也被称为杆,是首先***患者的血管中的部分。所述导管1具有外壁2及两个端部:端部3(A部侧)和端部4(C部侧)。导管1的B部在外壁2中具有凹部5。所述凹部5沿B部的长度方向延伸并且存在于导管1的整个外周。由于此凹部5的存在,导管1的A部和C部具有基本相同的直径,而B部则具有较小直径。可膨胀的膨胀囊6如在现有技术中那样设置,即例如粘接在导管1的凹部5中。凹部5使得装配有收缩的膨胀囊的导管B部的直径基本等于A部和C部直径。在导管1内部插有金属导向件7。结合在导管1的壁中的流体连接端口8将可膨胀的膨胀囊6与图1和图2中示意性表示的端部4处的充胀装置9连接,所述充胀装置9可以是操纵器。
在图1中,膨胀囊6收缩;因此,带有收缩的膨胀囊6的导管1的B部直径基本等于导管1的A部和C部的直径。
在图2中,膨胀囊6膨胀,此时带有膨胀的膨胀囊6的导管1的B部直径大于导管1的A部和C部的直径。
下面描述根据本发明的搏动装置的***。用针在患者血管之一上刺出开口或***点。之后装入金属导向件7。然后用所述导向件7将导管1通过所述开口***。导管1的A部、B部和C部相继通过此开口,由于上文所述的A部、C部与装配有收缩的膨胀囊6的B部具有基本相同的直径,所以不会引起所述开口的任何扩大。一旦导管1就位,即一旦膨胀囊6占据了将要治疗的血管区域,则***点被导管C部完全填充,从而减少血流并止血。
图3表示连接于充胀装置9的一种特别的实施方式的图2中的导管1。
所述充胀装置9包括:
-第一部,所述第一部包括充满流体11的囊袋10,所述囊袋10一端连接于流体连接端口8,另一端则连接于止回阀12,以及
-第二部,所述第二部包括所述囊袋10的压缩装置13,所述压缩装置13包括囊袋压缩室14以及压缩室14的控制器15,该控制器15例如是电动机械型。所述囊袋压缩室示意性地表示成大体为矩形,所述矩形具有两长边C1,而两短边之一C2敞开,另一短边C3连接至用三角形示意性表示的电动机械控制器15。压缩室14因此具有凹部16。
如上所述,根据本发明的导管1被***患者血管中。流体连接端口8的从患者身体凸出的端部连接至囊袋10。之后通过打开所述阀12将流体11(可以是氦、二氧化碳、生理盐溶液)注入囊袋10(此操作可在将流体连接端口8连接至囊袋10之前进行)。然后将囊袋10***由电动机械装置控制器15控制的压缩室14的凹部16内。根据由所述电动机械装置控制器15接收的指令建立精确的囊袋10的压缩/解压缩比率,此比率例如可以是10至300次压缩/分钟。囊袋10的压缩使得流体11朝向膨胀后的膨胀囊6流动,而囊袋10的解压缩使得流体11从膨胀囊6吸入至囊袋10,这使得膨胀囊收缩。由此将流体的搏动从囊袋10传递到膨胀囊6。因而此导管-膨胀囊-充胀装置组件(如图3描述的)形成了便携式搏动医疗组件。确实,包括囊袋10、囊袋压缩室14和电动机械控制器15的充胀装置可以被患者在移动时很容易地携带,使患者能保持某种程度的活动性。
所述充胀装置廉价易用。确实,压缩/解压缩不需要很昂贵的压力源,与根据现有技术的动脉内膨胀囊不同。
由于根据本发明的搏动装置可以应用于小直径导管,因此与现有情况不同,可使用小型搏动导管。这些小型搏动导管可以在很多应用中使用。
确实,本发明人意外地发现使***血管中的膨胀囊膨胀增加了血管壁的剪切强度。
因此,这些小型搏动导管不仅可以用于治疗冠状动脉阻塞(最小的导管直径使得能够到达动脉阻塞区域,而膨胀囊的搏动能够对所述区域进行轻柔的治疗),还可以通过脐血管治疗可能的胎儿畸形。可以设想许多其他应用,例如血管再生-细胞凋亡的相互依存关系(例如在老年人发生骨折的情况下增加血管再生以加速愈合)、(冠状动脉、脑部的、肾脏的)动脉粥样硬化、免疫***、心脏发生、一氧化氮分泌(例如用于***性或急性治疗、最重要的是慢性肺动脉高血压)。
Claims (10)
1.一种搏动医疗装置,其包括:
导管(1),所述导管(1)将被***血管中,所述导管(1)具有直径且包括:
一个称为A部的***端部,该***端部具有杆,以及
一个称为C部的端部,所述称为C部的端部与所述A部相对;
可膨胀部件(6),所述可膨胀部件(6)被容纳在所述导管(1)的位于所述A部与所述C部之间的称为B部的部分的周围,所述可膨胀部件(6)设计成连接至定位在所述C部处的充胀装置(9),从而使所述可膨胀部件能够以脉冲方式膨胀/收缩,
其特征在于,所述B部在所述导管的外壁中具有凹部(5),使得所述导管(1)的B部的直径小于所述导管(1)的A部和C部的直径,并且,所述导管(1)的A部和C部的直径基本相等,并且所述可膨胀部件(6)定位在所述凹部(5)中。
2.如权利要求1所述的搏动医疗装置,其特征在于,所述导管(1)的B部加上收缩的所述可膨胀部件(6)的直径小于或等于所述导管(1)的A部和C部的直径。
3.如权利要求1或2所述的搏动医疗装置,其特征在于,所述可膨胀部件(6)是膨胀囊。
4.如权利要求1或2所述的搏动医疗装置,其特征在于,所述可膨胀部件(6)由生物适应性的辐射透不过的材料形成。
5.如权利要求4所述的搏动医疗装置,其特征在于,所述材料是聚氨酯。
6.如权利要求1或2所述的搏动医疗装置,其特征在于,所述导管(1)的直径为几毫米或更小。
7.如权利要求1或2所述的搏动医疗装置,其特征在于,所述可膨胀部件(6)的尺寸为长度在0.1cm至2cm之间、体积在0.1cm3至2cm3之间。
8.一种包括如前述权利要求中任一项所述的搏动医疗装置及充胀装置(9)的便携式搏动医疗组件,其包括:
囊袋(10),所述囊袋(10)适于被填充流体(11),
囊袋压缩装置(14),所述囊袋压缩装置(14)适于以脉冲方式压缩所述囊袋(10);以及
连接装置(8),所述连接装置(8)将所述囊袋(10)连接至所述导管的所述可膨胀部件(6),使得所述流体(11)能够在所述可膨胀部件(6)与所述囊袋(10)之间循环。
9.如权利要求8所述的便携式搏动医疗组件,其特征在于,所述囊袋压缩装置(14)以电动机械的方式受控(15)。
10.如权利要求8或9所述的便携式搏动医疗组件,其特征在于,所述搏动医疗装置和所述充胀装置是一体的。
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FR0801816 | 2008-04-02 | ||
FR0801816A FR2929523B1 (fr) | 2008-04-02 | 2008-04-02 | Nouveau dispositif medical pulsatile |
PCT/FR2009/050564 WO2009136034A2 (fr) | 2008-04-02 | 2009-04-02 | Nouveau dispositif medical pulsatile |
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CN101983077B true CN101983077B (zh) | 2014-09-17 |
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US (1) | US8333731B2 (zh) |
EP (1) | EP2268336B1 (zh) |
JP (1) | JP5698653B2 (zh) |
CN (1) | CN101983077B (zh) |
BR (1) | BRPI0906299A2 (zh) |
DK (1) | DK2268336T3 (zh) |
ES (1) | ES2539839T3 (zh) |
FR (1) | FR2929523B1 (zh) |
HU (1) | HUE025575T2 (zh) |
PL (1) | PL2268336T3 (zh) |
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US8684903B2 (en) | 2011-03-11 | 2014-04-01 | Gui Fu WU | Therapeutic and surgical treatment method for providing cardiopulmonary and circulatory assist device |
CN105407829A (zh) | 2013-06-12 | 2016-03-16 | 萨亚德·诺尔 | 用于医疗设备的定位*** |
JP7200447B2 (ja) * | 2016-10-25 | 2023-01-10 | マフィン・インコーポレイテッド | 脈管定着式導入器シース |
US11541204B2 (en) * | 2018-09-26 | 2023-01-03 | W. L. Gore & Associates, Inc. | Cyclic expansion tissue treatment programs and associated systems |
CN110292678B (zh) * | 2019-08-12 | 2021-05-18 | 河南科技大学第一附属医院 | 一种搏动性输血装置 |
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- 2009-04-02 CN CN200980112207.5A patent/CN101983077B/zh not_active Expired - Fee Related
- 2009-04-02 HU HUE09742232A patent/HUE025575T2/en unknown
- 2009-04-02 PT PT97422323T patent/PT2268336E/pt unknown
- 2009-04-02 EP EP09742232.3A patent/EP2268336B1/fr not_active Not-in-force
- 2009-04-02 PL PL09742232T patent/PL2268336T3/pl unknown
- 2009-04-02 BR BRPI0906299-8A patent/BRPI0906299A2/pt not_active Application Discontinuation
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- 2009-04-02 WO PCT/FR2009/050564 patent/WO2009136034A2/fr active Application Filing
- 2009-04-02 ES ES09742232.3T patent/ES2539839T3/es active Active
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BRPI0906299A2 (pt) | 2015-08-11 |
WO2009136034A3 (fr) | 2009-12-30 |
EP2268336A2 (fr) | 2011-01-05 |
HUE025575T2 (en) | 2016-04-28 |
JP2011516139A (ja) | 2011-05-26 |
PL2268336T3 (pl) | 2015-12-31 |
CN101983077A (zh) | 2011-03-02 |
US8333731B2 (en) | 2012-12-18 |
ES2539839T3 (es) | 2015-07-06 |
WO2009136034A2 (fr) | 2009-11-12 |
DK2268336T3 (en) | 2015-07-06 |
FR2929523B1 (fr) | 2011-04-15 |
FR2929523A1 (fr) | 2009-10-09 |
PT2268336E (pt) | 2015-07-16 |
JP5698653B2 (ja) | 2015-04-08 |
EP2268336B1 (fr) | 2015-03-25 |
US20110021987A1 (en) | 2011-01-27 |
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