CN1933771A - 利用单个电感器的开关模式血氧计led驱动 - Google Patents
利用单个电感器的开关模式血氧计led驱动 Download PDFInfo
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- A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
- A61B5/14551—Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue using optical sensors, e.g. spectral photometrical oximeters for measuring blood gases
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Abstract
本发明提供一种用于一血氧计的光发射器驱动电路,其利用一单个电感器(L6)以驱动多个光发射器(50)。所述电感器连接到一开关电路(40)且连接到例如电容器的多个能量存储电路。这些能量存储电路通过使用相同电感器而交替充电。随后,所述电容器通过相同电感器交替放电以用于它们相应的光发射器。而且,通过使用在电感器中的磁通量消除来降低LED驱动电路的磁化率。在一个实施例中,使用一在其磁通量中具有几何对称性的环形电感器。在另一个实施例中,使用双芯闭合绕线管屏蔽电感器。
Description
技术领域
本发明涉及血氧计,且特定而言,涉及脉冲血氧计中的LED驱动电路。
背景技术
脉冲血氧定量法通常用于测量各种血液化学特征,包括(但不限于):动脉血中血红蛋白的血氧饱和度、供应给组织的个别血液脉动的体积,和对应于患者的每一次心跳的血液脉动率。这些特征的测量已由使用非侵入性传感器来完成,所述传感器将光散射而穿过患者组织中有血液灌注到组织的一部分中,且光电地感测光在上述组织中的吸收。以不同波长吸收的光的量接着用来计算所测量的血液成分的量。
选择散射过组织的光以具有一个或一个以上的波长,其由血液吸收且吸收数量表示血液中的血液成分的量。所传输散射过组织的光的量将根据组织中的血液成分的变化量和相关的光吸收而改变。根据用于测量血氧饱和度的已知技术,为测量血氧含量,这些传感器通常已具有适用于产生具有至少两种不同波长的光的光源,且具有对那两种波长敏感的光电检测器。
已知非侵入性传感器包括紧固到身体的一部分(例如,手指、耳朵或头皮)上的装置。在动物和人类中,这些身体部分的组织灌注有血液并且组织表面易于由传感器所接近。
通常为发光二极管(LED)的光源,需要由电流驱动以激活它们。由于需要大量的电流,因此,这可干扰降低血氧计所消耗的功率。在美国专利第6,226,539号中展示一种解决方案。其中,首先使用一电感器和电容器电路来将电荷存储在一第一开关位置上,并且,随后,在一第二开关位置上,将所存储的电荷传递给LED。使用两种不同的电感器和电容器电路,为每一LED使用一种电路。将需要减少在本专利的电路中所需的组件的数量。
发明内容
本发明提供一种用于一血氧计的光发射器驱动电路,其利用一单个电感器以驱动多个光发射器。所述电感器通过一个开关电路连接到如电容器的多个能量存储电路。这些能量存储电路通过使用相同电感器而交替充电。随后,所述电容器通过相同电感器交替放电以激活它们相应的光发射器。
在本发明的另一个方面中,通过使用在电感器中的磁通量消除来降低LED驱动电路的磁化率。在一个实施例中,使用在其磁通量中具有几何对称性的环形电感器。在另一个实施例中,使用双芯闭合绕线管屏蔽电感器(dual core closed bobbin shieldedinductor)。这个实施例具有串联的两芯的绕组,其用于消除外部磁场的效应。
为了进一步理解本发明的性质和优点,可参考结合附图所说明的以下实施方式。
附图说明
图1是并入本发明的血氧计的方框图。
图2是根据本发明的一个实施例的LED驱动电路的电路图。
图3是用于产生图2电路的定时和控制信号的逻辑的一个实施例的方框图。
图4是用于本发明的一个实施例中的环形电感器的图。
图5和图6是根据本发明的一个实施例的双芯电感器的图。
具体实施方式
图1说明并入本发明的血氧定量法系统的实施例。传感器10包括红光LED和红外光LED以及光电检测器。电缆12将它们连接到电路板14。由一LED驱动接口16提供LED驱动电流。将从传感器接收到的光电流提供到一I-V接口18。随后将IR电压和红光电压提供到一并入本发明的∑-Δ接口20。将∑-Δ接口20的输出提供给一微控制器22。微控制器22包括用于程序的闪存,和用于数据的SRAM存储器。处理器也包括一个连接到闪存26的控制器芯片24。最后,使用一个时钟28并且提供一个接口30以用于传感器10中的数字校准。一独立主机32接收经处理的信息,并且在线34上接收一模拟信号以用于提供模拟显示。
LED驱动电路
图2是根据本发明的一个实施例的LED驱动电路的电路图,其形成图1的LED驱动接口16的一部分。电压调节器36提供一个与整个血氧计电路的电源电压分离的电压。将在线38上的4.5伏信号提供为输出,其中电平是由电阻器R89和R90的反馈电阻分压器设置。线38上的电压提供给FET晶体管Q11且提供给电感器L6。通过电感器L6的电流由开关40提供到电容器C65和C66中的一个,其中所述电容器C65和C66分别存储用于红光LED和IR LED的电荷。线42上的红光/IR控制信号在血氧计处理器的控制下选择开关位置。线44上的控制信号LED PWM门控可控制晶体管开关Q11的开关。
一旦电容器被充电,那么线44上的控制信号关闭Q11并且将来自电容器C65或C66的电流通过开关40和电感器L6分别通过晶体管Q5和Q6提供到红光阳极线46或IR阳极线48。一信号“红光门控”接通晶体管Q5,而其反向“/红光门控”关闭晶体管Q7。这提供通过红光阳极线46到达背对背LED 50的电流,其中电流通过IR阳极返回且到达晶体管Q8,并且通过电阻器R10到达大地。晶体管Q8由信号“/IR门控”接通,而这一信号的反向“IR门控”关闭晶体管Q6。当驱动IR阳极时所述信号翻转,其中“IR门控”和“红光门控”信号以及它们的反向改变状态,使得电流通过晶体管Q6提供到IR阳极48,并且通过红光阳极46并通过晶体管Q7返回到电阻器R10和大地。读取“LED电流感测”信号用于与本发明不相关的校准目的。
当将来自电容器C65或C66的电流通过电感器L6提供到LED,并且在需要时切断所述电流时,晶体管Q11接通,使得在过渡期间的剩余电流可转储到电容器C64中。这解决FET晶体管开关并非为瞬时的事实。接着,C64通过Q11和电感器L6将其电流转储到重新充电时的电容器中。
电阻器R38和电容器C67是并联连接到电感器L6来防止信号尖峰,并且提供一个平滑过渡。连接到电感器L6的是具有一个由线54上的LED取样保持信号控制的开关52的取样电路,以对信号进行取样,并且将其通过放大器56提供到由处理器读取的线58上的“LED电流”信号。运算放大器56在4.5伏特与大地电压之间运算。因此,将稍微高于大地电压的参考电压(0.2伏)提供为引脚3的参考电压。提供一个积分电容器C68,使其与放大器56并联。一开关60响应于“清除LED取样”信号来操作开关,以在取样之间使电容器短路。
取样与保持电路测量电容器C69与电感器L6之间的节点T18处的电压,以确定电流。电容器C69是电容器C65和C66的值的1/1000。因此,通过C69提供比例电流,所述比例电流通过开关52注入到积分电容器C68中,以提供可在线58上的放大器56的输出处测量的电压。在线58上由处理器测量的电压用作一个反馈,其中所述处理器改变传递到晶体管Q11的脉冲的宽度,以选择性地改变传递给电容器65和66的能量的量,并且随后最终放电到LED 50中。在处理器内部的PI(比例积分)回路随后控制Q11处的PWM信号。这允许对LED强度进行精确控制,从而允许其最大化(如果需要),而不会超过期望限度(以避免灼伤患者等)。
图的左下方展示一个“4.5v LED禁用”信号,其由微处理器使用以在特定情况下关闭电压调节器36。例如,如果在LED线上存在问题,那么寻找在插入的新传感器中的短路的诊断将关闭电压调节器。
图3说明从图1上看,连接到图1中的LED驱动接口中的程序化逻辑62的处理器22。程序化逻辑62响应于来自时钟、同步脉冲和脉冲宽度信号的处理器的基本定时信号,来提供由图2的电路使用的不同控制信号。
因此,本发明通过在电感器与电容器之间移动开关位置来消除对于两个电感器的需求,而提供对专利第6,226,539号中所示的电路的改进。这不仅减少了零件数量(仅需要一个电感器而不是两个电感器),而且还提供红光驱动电流与IR驱动电流之间的更好的匹配,因为两者都使用相同电感器。
在本发明的另一方面中,降低了LED驱动电路对磁干扰的敏感性。这一磁干扰可使所检测的血容积描述波形(pleth waveform)失真。这通过使用电感器中的磁通量消除来最小化。在一个实施例中,这为图4中所展示的环形电感器。所述环形电感器在其磁通量上具有几何对称性。另一个实施例使用如图5和图6中所展示的双芯闭合绕线管屏蔽电感器。串联的两芯的绕组用来消除外部磁场的效应。这些磁通量消除电感器可用于图2的电路中,或者可用于现有技术的双电感器实施例中。图5展示在圆柱体72中具有一个绕线管70的双芯电感器。如图6中所示,导线通过间隙76缠绕。第一绕组78是顺时针的,而第二绕组80是逆时针的。还展示了俯视图82。理想地,在一个实施例中的组合电感为680uH。
在图2的实施例中所说明的本发明能够通过H桥接拓扑结构将电流多路传输给背对背LED。或者,可提供不同数量的负载。本发明可缩放为N个负载。本发明通过支撑组件的减少、组件的选择以及“更少损失”电容器和电感器存储装置的性质而提供显著效率。图2的电路可处理在LED上的大范围的正向电压降。所提供的电压根据LED电压降而自动发生变化,并且不会产生多于其所需要产生的能量。
通过处理器中的PI回路动态控制所述电路,其中电流反馈是由每一存储电容器(C65和C66)形成的电容性分流器提供,这提供隔离。所述反馈可由一传统的串联的感测电阻器R10校准。另外,这一技术允许在取样周期期间调整峰值电流以得到最佳信噪比。
添加上游线性调节器36增强电源供应抑制能力,而PI回路提供(对漂移、P-P、电涌等的)额外电源供应不敏感性。
如所属领域的技术人员将了解,本发明可以其它特定形式体现,而不脱离本发明的本质特征。例如,可通过添加另一引脚,其中FET晶体管开关连接到电感器,而提供三条驱动线(而不是两条驱动线)。另外,这可缩放为并联连接的三个以上的引脚,类似于Q6、Q8的引脚和Q5、Q7的引脚。因此,前述描述意在对以上权利要求书中所阐述的本发明的范畴进行说明而非限制。
Claims (15)
1.一种用于一血氧计的光发射器驱动电路,其包含:
一电压产生电路;
一电感器,其耦合到所述电压产生电路;
一第一开关电路,其耦合到所述电感器的一第一节点;
第一能量存储电路和第二能量存储电路,其连接到所述第一开关电路,使得来自所述电感器的电流可由所述第一开关电路导引到所述能量存储电路中的一者;
一第二开关电路,其耦合到所述电感器的一第二节点;和
第一光发射器驱动线和第二光发射器驱动线,其连接到所述第二开关电路,使得来自所述第一能量存储电路和所述第二能量存储电路的能量可交替耦合到所述第一光发射器驱动线和所述第二光发射器驱动线。
2.根据权利要求1所述的电路,其中所述第一能量存储电路和所述第二能量存储电路包含第一电容器和第二电容器。
3.根据权利要求1所述的电路,其中所述驱动线经配置以驱动背对背的光发射器。
4.根据权利要求3所述的电路,其中所述第二开关电路是一包括四个晶体管的H桥接驱动电路。
5.根据权利要求1所述的电路,其中所述电压产生电路是一与用于所述血氧计的一剩余者的一电源电压分离的电压调节器。
6.根据权利要求1所述的电路,其进一步包含一电阻器和一电容器,所述电阻器和所述电容器与所述电感器并联。
7.根据权利要求1所述的电路,其中所述电感器是一磁通量消除电感器。
8.根据权利要求7所述的电路,其中所述电感器是一环形电感器。
9.根据权利要求7所述的电路,其中所述电感器是一双芯闭合绕线管屏蔽电感器。
10.根据权利要求1所述的电路,其进一步包含一取样与保持电路,所述取样与保持电路连接到所述电感器的所述第二节点。
11.根据权利要求1所述的电路,其进一步包含至少一第三能量存储电路。
12.一种用于一血氧计的LED电路,其包含:
一电压产生电路;
一电感器,其耦合到所述电压产生电路;
一第一开关电路,其耦合到所述电感器的一第一节点;
第一电容器与第二电容器,其连接到所述第一开关电路,使得来自所述电感器的电流可由所述第一开关电路导引到所述电容器中的一者;
一H桥接驱动开关电路,其包括耦合到所述电感器的一第二节点的四个晶体管;和
第一光发射器驱动线和第二光发射器驱动线,其用于在所述H桥接中间的呈一背对背构形的LED,使得来自所述第一电容器和所述第二电容器的能量可交替耦合到所述第一光发射器驱动线和所述第二光发射器驱动线。
13.一种用于一血氧计的光发射器驱动电路,其包含:
一电压产生电路;
第一能量存储电路和第二能量存储电路;
一磁通量消除电感器,其耦合到所述电压产生电路和所述能量存储电路中的至少一者;和
开关电路,其经配置以首先将电流导引到所述能量存储电路中,且随后将来自所述第一能量存储电路和所述第二能量存储电路的能量提供给用于光发射器的驱动线。
14.根据权利要求12所述的电路,其中所述电感器是一环形电感器。
15.根据权利要求12所述的电路,其中所述电感器是一双芯闭合绕线管屏蔽电感器。
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US10/787,852 | 2004-02-25 | ||
US10/787,852 US7120479B2 (en) | 2004-02-25 | 2004-02-25 | Switch-mode oximeter LED drive with a single inductor |
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EP (1) | EP1722673B1 (zh) |
JP (1) | JP4676979B2 (zh) |
KR (1) | KR20070026417A (zh) |
CN (1) | CN1933771A (zh) |
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AU (1) | AU2005216975A1 (zh) |
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US7551950B2 (en) | 2004-06-29 | 2009-06-23 | O2 Medtech, Inc,. | Optical apparatus and method of use for non-invasive tomographic scan of biological tissues |
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-
2004
- 2004-02-25 US US10/787,852 patent/US7120479B2/en active Active
-
2005
- 2005-02-25 ES ES05723886T patent/ES2326231T3/es active Active
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- 2005-02-25 DE DE602005014091T patent/DE602005014091D1/de active Active
- 2005-02-25 JP JP2007501031A patent/JP4676979B2/ja active Active
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- 2005-02-25 CA CA2556720A patent/CA2556720C/en active Active
- 2005-02-25 CN CNA2005800058618A patent/CN1933771A/zh active Pending
- 2005-02-25 KR KR1020067018682A patent/KR20070026417A/ko not_active Application Discontinuation
- 2005-02-25 WO PCT/US2005/006207 patent/WO2005082239A1/en active Application Filing
- 2005-02-25 AT AT05723886T patent/ATE429172T1/de not_active IP Right Cessation
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Cited By (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
CN107106023A (zh) * | 2014-11-20 | 2017-08-29 | 高通股份有限公司 | 允许能够确定血属性的设备的低电流操作的电路 |
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CA2556720A1 (en) | 2005-09-09 |
EP1722673A1 (en) | 2006-11-22 |
US8195262B2 (en) | 2012-06-05 |
US7120479B2 (en) | 2006-10-10 |
JP4676979B2 (ja) | 2011-04-27 |
US20060264720A1 (en) | 2006-11-23 |
ES2326231T3 (es) | 2009-10-05 |
CA2556720C (en) | 2013-05-14 |
US20050187447A1 (en) | 2005-08-25 |
DE602005014091D1 (de) | 2009-06-04 |
ATE429172T1 (de) | 2009-05-15 |
WO2005082239A1 (en) | 2005-09-09 |
AU2005216975A1 (en) | 2005-09-09 |
MXPA06009750A (es) | 2007-03-15 |
EP1722673B1 (en) | 2009-04-22 |
JP2007525292A (ja) | 2007-09-06 |
KR20070026417A (ko) | 2007-03-08 |
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