中國醫藥大學機構典藏 China Medical University Repository, Taiwan:Item 310903500/25297

行政院國家科學委員會專題研究計畫 成果報告

生醫電訊號之互補式金氧半積體電路設計

計畫類別： 個別型計畫

計畫編號：

NSC91-2213-E-039-002-執行期間： 91 年 08 月 01 日至 92 年 07 月 31 日

執行單位： 中國醫藥大學學士後中醫系

計畫主持人： 林育德

計畫參與人員： 李皖琦 劉芸澧 林東龍 徐雍智

報告類型： 精簡報告

處理方式： 本計畫可公開查詢

中

華

民

國 92 年 9 月 8 日

行政院國家科學委員會補助專題研究計畫成果

報告

※※※※※※※※※※※※※※※※※※※※※※※

※※

※

※

※ 生醫電訊號之互補式金氧半積體電路設計 (I)

※

※

CMOS integrated circuit design for biopotential amplifier (I)

※

※

※

※※※※※※※※※※※※※※※※※※※※※※※

※※

計畫類別：█個別型計畫

□整合型計畫

計畫編號：NSC 91－2213－E－039－002－

執行期間：91 年 8 月 1 日至 92 年 7 月 31 日

計畫主持人：林育德

本成果報告包括以下應繳交之附件：

□赴國外出差或研習心得報告一份

□赴大陸地區出差或研習心得報告一份

□出席國際學術會議心得報告及發表之論文各一份

□國際合作研究計畫國外研究報告書一份

執行單位：中國醫藥學院 學士後中醫系

中

華

民

國 92 年 9 月 4 日

行政院國家科學委員會專題研究計畫成果報告

生醫電訊號之互補式金氧半積體電路設計 (I)

CMOS integrated circuit design for biopotential amplifier (I)

計畫編號：NSC 91-2213-E-039-002

執行期限：91 年 8 月 1 日至 92 年 7 月 31 日

主持人：林育德 逢甲大學 自動控制工程學系

Email:

[email protected]

TEL: (04) 2451-7250 ext 3925

一、中文摘要

生醫電信號之種類很多，這些信號在醫

學臨床和基礎研究上均非常重要。欲量測

這些信號，必需有生醫電信號放大器的協

助才行，但是生醫電信號的振幅與頻率範

圍各異，而且生醫電信號相當微弱，在量

測生醫電信號時，容易受到干擾而影響信

號品質。所以欲設計符合需求之高品質生

醫電信號放大器，需要對干擾的產生機

制、電極特性與信號的特性充分了解，因

此，這類放大器的設計往往需要豐富的設

計經驗。為使設計更具效率，最好的辦法

就是藉由功能強大之電腦輔助設計工具的

協助，設計與模擬均在此工具中完成，如

此可節省開發時間和成本。本研究為了達

成此一目標，在本年度的執行進度中，首

先是提出了包含模擬生醫電信號產生源、

實際等效電路的皮膚電極阻抗以及模擬外

在干擾的生醫電信號量測的 Spice 模擬模

型，為了驗證此模型是否合理，本研究利

用此模型設計一個心電信號的放大器，比

較此放大器的模擬特性和實際特性，以及

心電信號放大的模擬結果和實際量測結

果，結果是放大器的模擬特性和實際電路

的特性相差無幾，而且對於生醫電信號量

測常遭遇到的電源干擾可以合理地反映出

其所受之影響。由於心電信號具有 QRS

波，驗證容易，所以本研究舉此為例，同

樣的模型原理也可以應用到其它的生醫電

信號的量測上。

關鍵詞：生醫電信號放大器、電腦輔助設

計、皮膚電極阻抗、心電信號、電源干擾、

Spice、QRS 波

Abstr act

A special circuit named as biopotential amplifier is needed for measuring specific bioelectric signal. The magnitude and frequency range differ for different biopotential signals. Besides, biopotential signals are tiny in amplitude and the measurement is easily corrupted by external interference. For these reasons, the design of high-quality biopotential amplifier is usually an empirical task. To make the design more efficient, this study proposes a simulation model for bioelectric signal measurement such that the design of biopotential amplifier can be achieved by powerful computer-aided design (CAD) tool, where few studies have reported on such a topic. The proposed model is based upon previously published literatures with two distinct features added. The first feature is the genesis methodology of simulated biopotential signal. The second one is the skin-electrode impedance is replaced by the corresponding equivalent circuit of a complex RC network. To verify the feasibility of the proposed model, an ECG amplifier (in three-electrode/non-isolated configuration) is designed in Spice-related CAD tool and is implemented for ECG recording. From the results, the amplifier characteristics agree well between the simulated and the implemented circuit. Besides, the effect due to the commonly

encountered power-line interference during biopotential measure- ment can be reasonably evaluated in the proposed model. In this study, the model for ECG signal is selected for the distinguished feature of QRS complex, which will make the result verification easier. The same principle can be applied to the other kind of bioelectric signals and configuration modes.

Keywords:

biopotential

amplifier,

computer-aided

design

(CAD),

skin-electrode impedance, Spice, power-line

interference

1. Intr oduction

Bioelectric

signals

are

of

clinical

importance. These signals are tiny in

amplitude and usually may be disturbed by

external interference. A specialized amplifier

named as biopotential amplifier is needed for

the measurement of such signals. The design

criteria for such amplifier have been

discussed extensively in some literatures

(METTINGVANRIJN

et

al.,

1991;

NEUMAN, 1992b; METTINGVANRIJN et

al., 1994). As described in these studies,

much attention should be paid for the design

of such amplifier, and the designers should

be aware of the mechanisms of external

interference. Much work has been conducted

on the effects of external interference,

especially

the

commonly

encountered

power-line interference, during biopotential

measurement and the methods for reducing

such effects (HUHTA and WEBSTER, 1973;

WINTER and WEBSTER, 1983a; 1983b;

PALLÁ S-

ARENY,

1986;

1988;

METTINGVANRIJN et al., 1990; WOOD et

al., 1995; SPINELLI, 1999).

However, little research has been done on

the

computer-aided

design

(CAD)

of

biopotential

amplifier.

This

issue

is

extraordinarily

important

for

specific

applications in which commercial products

may be too bulky and expensive, such as

remote monitoring of vital signals and

wearable technology for healthcare (PARK

and JAYARAMAN, 2003). With the aid of

powerful circuit analysis software, e.g. Spice,

the task of amplifier design will be much

easier. To attain the goal of CAD for

biopotential amplifier, it is necessary to

establish a model that can generate simulated

biopotential signal and can simulate the

practical measurement conditions where the

complex skin-electrode impedance and the

effects due to nearby power lines should be

included. Using this model, the designer can

estimate the performance of the amplifier and

evaluate

the

influence

of

external

interference in circuit simulation package.

The development time can thus be saved and

the probability of design error can also be

reduced by this approach. The objective of

this paper is to propose a Spice model

owning the properties mentioned above, and

we also use this model to design a

three-electrode/non-isolated

electrocardiogram (ECG) amplifier. There is

a high level of agreement between the

simulation and practical measurement results

for both general and severer power-line

interference conditions. The proposed Spice

model is feasible for the simulation of

bioelectric signal measurement and will be

helpful for biopotential amplifier design.

Because

the

distinct

features

of

QRS-complex in ECG pattern, it is easier to

verify the evaluation results for the

amplification of ECG signal. The Spice

model that simulates the measurement of

ECG signal is thus adopted in this study. The

simulated ECG pattern in this model is

modified from MIT116, which is selected

randomly from MIT/BIH ECG database. The

same model can also be applied to the other

kind of bioelectric signal with the simulated

biopotential pattern being replaced by the

corresponding simulated signal.

2. The Spice model

To simplify the analysis, the measurement of bioelectric events can be depicted in a simplified equivalent circuit model as demonstrated in Figure 1 (a). In this figure, Zeq1 and Zeq2 denote the

skin-electrode impedance, ZDM is the

differential-mode input impedance of the biopotential amplifier, and ZCM1 and ZCM2 represent the

common-mode input impedance of the amplifier. Wood et al. (1995) have used pure resistance at a specific frequency for Zeq1 and Zeq2 to evaluate the

effects of displacement currents induced into the leads and the body in biopotential measurement. However, the skin- electrode interface is in fact a complex RC network (ROSELL et al., 1988; NEUMAN, 1992a), and its equivalent circuit model is as shown in Figure 1 (b), in which the model for popular Ag/AgCl electrode is used. In Figure 1 (b), Ehc is the half-cell

impedance associated with the electrode-electrolyte interface and polarization effects, and Rs comes from the effective resistance associated with interface effects of the conduction gel between the electrode and the skin. The difference in ionic concentration across epidermis forms the potential difference Ese.

The epidermal layer is found to behave as an electrical impedance of a parallel RC circuit (Re||Ce). In the dermis and the subcutaneous layer, the impedance can be represented as pure resistance (Ru). The impedance value depends upon many factors, such as skin condition and preparation, type of conduction gel and the attachment status of electrodes, and so on. Clearly, the skin-electrode impedance will also change with different frequency, and the DC offset voltage of the electrodes (Ehc and Ese) may cause saturation of

amplifier if not dealt with properly. The simple resistance model cannot reflect such information, therefore the model shown in Figure 1 (b) is recommended for Zeq1 and Zeq2 in circuit design, and it

is also adopted in our study.

Replacing Zeq1 and Zeq2 of Figure 1 (a) by the

equivalent circuit model depicted in Figure 1 (b), we can observe the frequency response of

bio in

V

V

to evaluate the influence come from the impedance property of Zeq1 and Zeq2. The result is shown in Figure

2. From this result, the magnitude and phase of

bio in

V

V

will change with frequency, but the deviation is little. It is thus reasonable to generate the simulated biopotential, Vbio, from the measured biopotential

divided by the amplifier’s gain. In this study, MIT116 (an ECG signal selected randomly from MIT/BIH database) is used to serve the purpose, and a part of the pattern is demonstrated in Figure 3. All of the simulation in this study were carried out using Pspice A/D® in OrCAD® Family Release 9.2, and Pspice® Stimulus Editor is used to generate the simulated biopotential pattern in our study, where Pspice® and OrCAD® are registered trademarks of Cadence Design Systems, Inc.

One major problem encountered in biopotential recording is the appearance of unwanted power-line interference in the amplifier output (HUHTA and WEBSTER, 1973; WINTER and WEBSTER, 1983a; METTINGVANRIJN et al., 1990). There are four ways in which power lines can cause interference in biopotential measurement. 1) The magnetic field from power lines can cause an induced voltage in the loop formed by the electrode leads. 2) The electric field from power lines can induce a displacement current into the electrode leads which flows through the patient and thus creates an interfering voltage drop across the skin-electrode impedances. 3) The capacitively coupled displacement current can also flow into the patient and raise the common-mode potential with respect to both ground and circuit common. 4) The displacement current induced into the patient also creates an interference voltage between the recording electrodes as it flows through the body

impedance (HUHTA and WEBSTER, 1973; WINTER and WEBSTER, 1983a). Because the magnetic interference can be reduced by twisting the leads together, it is not necessary to include item 1) in the simulation model. Thakor and Webster (1980) have reported the interference voltage of item 4) can be neglected because the internal body impedances are very small and also the body disperses much of the displacement current such that the current flowing directly between two electrodes is reduced. For the reasons, only item 2) and 3) need be included in the simulation model. The proposed simulation model is illustrated in Figure 4, where Zeq1,2 and Zeqr denote

skin-electrode impedances, C1,2 is the lead capacitance

between lead wire and circuit common, Cg denotes the

capacitive coupling of subject to ground, Cs denotes

the stray capacitance between circuit common and ground, Zs represents the isolation impedance, and

Vbio is the simulated biopotential signal. Besides, Id1,2

and Idr represent the displacement currents coupled

into input leads, and Ib is the displacement current

coupled into body. SW1 in Figure 4 is the switch to determine either two- or three-electrode system, and SW2 is the switch to determine either isolated or non-isolated amplifier. By selecting the positions of SW1 and SW2, four configurations can be determined. They are isolated or non-isolated systems, using either two or three electrodes.

The proposed model is based on previously published work (HUHTA and WEBSTER, 1973; THAKOR and WEBSTER, 1980; WOOD et al., 1995) and mimics the electrical environment during biopotential measurement, including the skin-electrode impedances, capacitive couplings to ground, displacement currents induced from mains power line. The significant features of our model include the generation of simulated biopotential signal (Vbio in Figure 3) and the RC network for

skin-electrode impedances (circuit model in Figure 1 (b)).

3. Results

3.1 An ECG amplifier designed according to the proposed model

We designed an ECG amplifier, in three-electrode/ non-isolated configuration, with the aid of the proposed model to verify its feasibility. The amplifier circuit is demonstrated in Figure 5 (a). Figure 5 (b) shows the magnitude and phase response of the circuit for both nominal and the worst-case (10% element’s deviation) analysis. Following construction of a prototype, bench tests were carried out which gave results that were in close agreement with those of the simulations. The test results show that the mid-band gain is about 501, the 3-dB bandwidth extends from about 0.09 Hz to 152 Hz, and the CMRR of the amplifier is 116 dB. The power consumption of the circuit is about 156 mW. We find the characteristics of implemented amplifier agree well with those in simulation.

3.2Simulation results Simulation results

In order to evaluate the effect of power-line interference, two interference environments were

tested with different current parameters, while the skin-electrode impedances were kept the same. It is assumed that the skin is well prepared and the skin and electrodes are in good-contact status, but there exists 10% element’s deviation. Figure 6 shows the simulation result for general power-line interference environment with the parameters as follows: Ib＝100

nA, Idr＝100 pA, Id1＝90 pA and Id2＝110 pA. For the

simulation of severer power-line interference, the parameters are changed to: Ib＝500 nA, Idr＝450 pA,

Id1＝550 pA and Id2＝500 pA. The simulation result is

demonstrated in Figure 7. Results for time and frequency domain are given in both simulations.

3.3Measurement results

A practical measurement result of the designed circuit is demonstrated in Figure 8, where a male subject aged 30 was positioned at about 1 meter from a power-line cable collector in a university laboratory for electronic circuit design. Except the related instruments for signal measurement, the other equipments and the fluorescent lights were all turned off during the ECG recording. For the case of severer power-line interference condition, the same subject participated in the ECG recording at the same laboratory, and was positioned closer to the power-line cable collector (about 50 cm away). All the equipments in the laboratory were turned on, but the fluorescent lights were still kept off during the measurement. The result at the latter condition is shown in Figure 9. As in simulation case, time- and frequency-domain results are given in both Figure 8 and Figure 9. Lead II ECG signals were recorded in both cases. The electrode leads were twisted and run close to the subject’s body. The signals were sampled and recorded using a National Instruments DAQ Card-6024E for PCMCIA data acquisition board at a sampling frequency of 360 Hz, for a time of approximately 5 minutes each time. For a brief appearance of distinct QRS-complex, only a short segment (2.5 seconds or so) is shown in both Figure 8 (a) and Figure 9 (a).

The effects due to the power-line interference can be verified by power level at 50/60 Hz in corresponding spectrum. From the comparison of Figure 6 (b) versus Figure 8 (b) and Figure 7 (b) versus Figure 9 (b), the effects for different level of power-line interference can be reasonably evaluated via the proposed model.

4. Conclusion and Discussion

The purpose of this study is to propose a

simulation model in Spice for bioelectric

signal measurement that will be beneficial

for the design of biopotential amplifier.

Using the proposed model, the circuit

designer can thus estimate the circuit

performance and evaluate the effects due to

power-line interference in circuit simulation

package. Both the development time and cost

can be reduced by this approach. Based upon

the previously published work, the proposed

model

emphasises

on

the

genesis

methodology of simulated biopotential and

the complex RC network model is used for

skin-electrode impedance. To verify the

feasibility of the proposed model, we design

an ECG amplifier with the aid of this model.

After construction of the prototype, the

circuit

characteristics

and

practical

applications have been conducted for final

verification. The results show that there

exists a high level of agreement in

characteristics between the implemented

circuit and the simulated one. Besides, the

effect of power-line interference can be

reasonably evaluated by computer simulation

via the proposed model, where such effect is

usually difficult to analyse by hand.

Result shown in Figure 2 implies there is

no

much

response

difference

among

frequencies

as

Z

eq1,2

(skin-electrode

impedances) of Figure 1 (a) being replaced

by complex RC network (Figure 1 (b)). It

seems reasonably a pure-resistance model

can be feasible for skin-electrode impedance.

However, the phase contribution from each

component in driven-right-leg (DRL) circuit

is critical and should be estimated as

accurately as possible to attain the circuit

stability analysis. Moreover, the complex RC

network

model

can

reflect

the

frequency-dependent

property

of

skin-electrode impedance. It is also critical to

evaluate the potential divider effect in

biopotential recording, which will convert

the common-mode interference potential into

differential-mode signal and is primarily due

to the impedances imbalance between

recording electrodes. Clearly the potential

divider effect will also vary with different

frequency, and the effect at the power-line

frequency is the most important one. Such

information will be lost if the pure-resistance

model is adopted. For the reasons, the

complex RC network model is strongly

recommended for skin-electrode impedances.

In this study, the model for popular

Ag/AgCl electrode is adopted. If dry

electrodes are used for signal recording, the

equivalent circuit model should be modified.

Besides, the parameters in the proposed

model

depend

upon

principally

the

preparation of skin, the contact of electrode

with skin, and the interference from mains

power supply. Most of the parameter values

adopted in the simulation have also appeared

in other previously published work. From the

comparison

between

simulation

and

measurement results, the adopted values

seem feasible.

There are four modes of configuration

for biopotential measurement, they are

two-or three- electrode/isolated two-or non-isolated

configuration. And, there exists different

kind of biopotential signals being of clinical

importance. To verify the feasibility of CAD

methodology for biopotential amplifier, only

one

type

of

configuration

(three-electrode/non-isolated) and only ECG

signal is selected to serve the purpose. The

same modelling principle can also be applied

to the other three configuration modes and

the other kind of biopotential signals.

Reference

DOBREV, D. and DASKALOV, I. (2002):

‘Two-electrode biopotential amplifier with

current-driven inputs,’

Med. Biol. Eng.

Comput., 40, pp. 122-127

HUHTA, J. C. and WEBSTER, J. G. (1973):

‘60-Hz

interference

in

electrocardiography,’

IEEE

Trans.,

BME-27, pp. 91-101

METTINGVANRIJN, A. C., PEPER, A. and

GRIMBERGEN,

C.

A.

(1990):

‘High-quality recording of bioelectric

events. Part 1: Interference reduction,

theory and practice,’

Med. Biol. Eng.

Comput., 28, pp. 389-397

METTINGVANRIJN, A. C., PEPER, A. and

GRIMBERGEN,

C.

A.

(1991):

‘High-quality recording of bioelectric

events. Part 2: Low-noise, low-power

multichannel amplifier design,’

ibid., 29,

pp. 433-440

METTINGVANRIJN, A. C., PEPER, A. and

GRIMBERGEN, C. A. (1994): ‘Amplifiers

for bioelectric events: a design with a

minimal number of parts,’

ibid., 32,

pp.305-310

NEUMAN, M. R. (1992a): ‘Biopotential

electrodes,’ in Webster, J. G. (Ed.):

‘Medical instrumentation: application and

design.’ (Houghton Mifflin Co., Boston) pp.

227-287

NEUMAN, M. R. (1992b): ‘Biopotential

amplifiers,’

ibid., pp. 288-353

PALLÁ S-ARENY, R. (1986): ‘On the

reduction of interference due to common

mode voltage in two-electrode biopotential

amplifiers,’

IEEE Trans., BME-33, pp.

1043- 1046

PALLÁ S-ARENY,

R.

(1988):

‘Interference-rejection characteristics of

biopotential amplifiers: a comparative

analysis,’

ibid., BME-35, pp. 953-959

PARK, S. and JAYARAMAN, S. (2003):

‘Enhancing the quality of life through

wearable technology,’

IEEE Eng. Med. Biol.

Mag., 22, pp. 41-48

ROSELL, J., COLOMINAS, J., RIU, P.,

PALLÁ S-ARENY, R. and WEBSTER, J. G.

(1988): ‘Skin impedance from 1 Hz to

1MHz,’

IEEE Trans., BME-35, pp.

649-651

SPINELLI, E. M., MARTÍNEZ, N. H. and

MAYOSKY, M. A. (1999): ‘A

trans-conductance driven-right-leg circuit,’

ibid.,

BME-46, pp. 1466-1470

THAKOR, N. V. and WEBSTER, J. G.

(1980): ‘Ground-free ECG recording with

two electrodes,’

ibid., BME-27, pp.

699-704

WINTER, B. B. and WEBSTER, J. G.

(1983a): ’Reduction of interference due to

common mode voltage in biopotential

amplifiers,’

ibid., BME-30, pp. 58-62

WINTER, B. B. and WEBSTER, J. G.

(1983b): ’Driven-right-leg circuit design,’

ibid., BME-30, pp. 62-66

WOOD, D. E., EWINS, D. J. and

BALACHANDRAN,

W.

(1995):

‘Comparative

analysis

of

power-line

interference

between

two-

or

three-electrode biopotential amplifier,’

Med.

Biol. Eng. Comput., 33, pp.63-68

Zeq1 Zeq2 ZDM ZCM1 ZCM2 Vbio Vin Front end of biopotential amplifier DIFF1 DIFF2

(a)

Ru Re Ce Ese Rs Rd Cd Ehc

(b)

Figure 1 (a) The simplified equivalent circuit

model, where Z

eq1

and Z

eq2

denote the

skin-electrode impedance, Z

DM

is the

differential-mode input impedance of the

biopotential amplifier, and Z

CM1

and Z

CM2

represent

the

common-mode

input

impedance of the amplifier. (b) The

equivalent circuit model of skin-electrode

impedance.

Figur e 2 The frequency response of

bio in

V

V

for Figure 1 (a), where Z

DM

＝Z

CM1

＝Z

CM2

＝

10G

Ω

|| 2pF, and Z

eq1

and Z

eq2

have been

replaced by the circuit model depicted in

Figure 1 (c) in three different conditions as

follows.

: skin has not been prepared, and the

imbalance of electrode-electrolyte impedance

is in the worst case,

: skin has been prepared, and the imbalance

of electrode-electrolyte impedance is in the

worst case,

: skin has been prepared, electrodes are

well attached, and the electrode-electrolyte

impedance is 10% deviation from the typical

value.

Figure 3 One segment of the simulated ECG

pattern modified from MIT116.

Zeq1 Zeq2 Vbio Zeqr SW1 Cg Cs _Zs SW2 Biopotential amplifier OUT ckt common Ground DIFF1 Reference Ib Id1 Id2 Idr DIFF2 C1 C2

Figure 4 The proposed Spice model for

bioelectric signal measurement, where the

circuit model depicted in Figure 1 (c) is used

for Z

eq1

and Z

eq2

, and one segment of V

bio

is

R3 150k VCC 0 VCC C4 0.1m U1 AD620/AD 6 3 2 5 7 4 1 8 OUT + - REF V+ V-RG1 RG2 0 R13 24.9k VEE VCC R14 10k DIFF1 OUT 0 C5 0.01u R1 150k 0 VCC 0 R9 1k R10 69k C9 1n C3 0.1m 0 R4 150k R5 67k V1 6Vdc U2A AD713/AD 3 2 4 11 1 + -V+ V-OUT C1 0.1m 0 VOUT VEE R2 150k 0 0 0 R7 1k C8 0.047u 0 VCC C2 0.1m DIFF2 R11 2.5k U2C AD713/AD 10 9 4 11 8 + -V+ V-OUT R12 24.9k C7 0.047u R15 1MEG R8 1k U2B AD713/AD 5 6 4 11 7 + -V+ V-OUT C6 0.01u V2 6Vdc Reference VEE R6 67k VEE VEE 0

(a)

(b)

Figure 5 (a) A biopotential amplifier that is

designed according to the proposed Spice

model. (b) The frequency response of the

biopotential amplifier.

: the result of worst-case analysis with 10%

deviation of element values,

: the result for nominal element values.

(a)

(b)

Figur e 6 Simulation result (a) in time

domain, and (b) in Fourier analysis for

general power-line interference environment.

(a)

(b)

Figur e 7 Simulation result (a) in time

domain, and (b) in Fourier analysis for

severer power-line interference environment.

(a)

(b)

Figure 8 Measurement result (a) in time

domain, and (b) in frequency domain for

general power-line interference environment.

(a)

(b)

Figure 9 Measurement result (a) in time

domain, and (b) in frequency domain for

severer power-line interference environment.

行政院國家科學委員會補助專題研究計畫

█ 成 果 報

告 □期

中進度

報

告

生醫電訊號之互補式金氧半積體電路設計 (I)

CMOS integrated circuit design for biopotential

amplifier (I)

計畫類別：

█

個別型計畫

□ 整合型計畫

計畫編號：NSC 91 － 2213 － E － 039 － 002 －

執行期間： 91 年 8 月 1 日 至 92 年 7 月 31 日

計畫主持人：林育德

共同主持人：

計畫參與人員： 李皖琦 劉芸澧 林東龍 徐雍智

成果報告類型(依經費核定清單規定繳交)：

█

精簡報告 □完整

報告

本成果報告包括以下應繳交之附件：

□赴國外出差或研習心得報告一份

□赴大陸地區出差或研習心得報告一份

□出席國際學術會議心得報告及發表之論文各一份

□國際合作研究計畫國外研究報告書一份

處理方式：除產學合作研究計畫、提升產業技術及人才培育研究

計畫、列管計畫及下列情形者外，得立即公開查詢

□涉及專利或其他智慧財產權，□一年□二年後可公開

查詢

執行單位：中國醫藥學院 學士後中醫學系

中 華 民 國 92

年

9 月

4

日

可供推廣之研發成果資料表

□ 可申請專利 □ 可技術移轉

日期：92 年

9 月 4 日

附件二

國科會補助計畫

計畫名稱：生醫電訊號之互補式金氧半積體電路設計 (I)

計畫主持人： 林育德

計畫編號：

NSC 91－2213－E－039－002－

學門領域：

醫學工程

技術/創作名稱

發明人/創作人

中文：

（100~500 字）

技術說明

英文：

可利用之產業

及

可開發之產品

技術特點

推廣及運用的價值

1.每項研發成果請填寫一式二份，一份隨成果報告送繳本會，一份送

貴單位研發成果推廣單位（如技術移轉中心）

。

2.本項研發成果若尚未申請專利，請勿揭露可申請專利之主要內容。

3.本表若不敷使用，請自行影印使用。