TWI690301B - Ultrasound probe and control method thereof - Google Patents
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Abstract
Description
本揭露係有關於一種超音波探頭,特別是一種多角度超音波探頭。The present disclosure relates to an ultrasonic probe, especially a multi-angle ultrasonic probe.
超音波探頭的量測距離的原理是利用訊號發射元件發出之超音波至一目標物,並利用訊號接收元件接收由目標物反射之回波訊號,再根據回波訊號計算超音波探頭與目標物之間的距離。The principle of measuring the distance of the ultrasonic probe is to use the ultrasonic wave emitted by the signal transmitting element to a target, and use the signal receiving element to receive the echo signal reflected by the target, and then calculate the ultrasonic probe and the target according to the echo signal the distance between.
然而,由於現有之超音波探頭之訊號發射元件設置於基板上的角度為固定,故只能有效量測特定距離範圍的目標物,故當超音波探頭與目標物之距離改變、過近或過深時,超音波探頭的量測精確度容易受到影響。例如,當超音波探頭與目標物之距離較近時,超音波探頭則容易有偵測盲區,因此無法有效地量測超音波探頭與目標物之間的距離或深度。However, since the angle of the signal transmitting element of the existing ultrasonic probe is fixed on the substrate, it can only effectively measure the target object in a specific distance range. Therefore, when the distance between the ultrasonic probe and the target object changes, is too close, or too When deep, the measurement accuracy of the ultrasonic probe is easily affected. For example, when the distance between the ultrasonic probe and the target is relatively short, the ultrasonic probe is likely to have a blind spot, so it is impossible to effectively measure the distance or depth between the ultrasonic probe and the target.
此外,當超音波探頭應用於量測血流速度等醫學應用時,由於不同病人可能有不同的體型,故也可能有不同的血管深度,故超音波探頭與血管之間的距離也不盡相同,故也容易有偵測盲區,因此超音波探頭也無法精確地量測不同病人的血流速度。In addition, when the ultrasound probe is used in medical applications such as measuring blood flow velocity, because different patients may have different body types, they may also have different blood vessel depths, so the distance between the ultrasound probe and the blood vessel is also different. Therefore, it is also easy to detect blind spots, so the ultrasound probe cannot accurately measure the blood flow velocity of different patients.
因此,如何提出一種超音波探頭,能夠有效改現有之超音波探頭的各種限制已成為一個刻不容緩的問題。Therefore, how to propose an ultrasonic probe that can effectively change the limitations of the existing ultrasonic probe has become an urgent issue.
有鑑於上述的問題,本揭露之其中一目的就是在提供一種超音波探頭及超音波探頭控制方法,以解決現有之超音波探頭的各種問題。In view of the above-mentioned problems, one of the purposes of the present disclosure is to provide an ultrasonic probe and an ultrasonic probe control method to solve various problems of the existing ultrasonic probe.
本揭露之一實施例提出一種超音波探頭,其包含接收端、發射端及控制器。接收端包含訊號接收元件。發射端包含複數個訊號發射元件,各個訊號發射元件與訊號接收元件之間具有夾角,且該些訊號發射元件與訊號接收元件之間的夾角彼此不同。控制器與發射端及接收端連接,並依序驅動該些訊號發射元件,再由訊號接收元件接收各個訊號發射元件之回波訊號。其中,控制器比較該些回波訊號並根據比較結果由該些訊號發射元件選擇其中之一者做為目標訊號發射元件,並根據目標訊號發射元件之回波訊號產生量測結果。An embodiment of the present disclosure provides an ultrasonic probe, which includes a receiving end, a transmitting end, and a controller. The receiving end includes a signal receiving element. The transmitting end includes a plurality of signal transmitting elements, each of which has an angle between the signal transmitting element and the signal receiving element, and the angle between the signal transmitting element and the signal receiving element is different from each other. The controller is connected to the transmitting end and the receiving end, and drives the signal transmitting elements in sequence, and then the signal receiving element receives the echo signals of each signal transmitting element. The controller compares the echo signals and selects one of the signal transmitting elements as the target signal transmitting element according to the comparison result, and generates a measurement result according to the echo signal of the target signal transmitting element.
本揭露之一實施例提出一種超音波探頭控制方法,其包含下列步驟:透過控制器依序驅動發射端之複數個訊號發射元件,各個訊號發射元件與接收端之訊號接收元件之間具有夾角,且該些訊號發射元件與訊號接收元件之間的夾角彼此不同;由訊號接收元件接收各個訊號發射元件之回波訊號,並傳送至控制器;由控制器比較該些回波訊號並根據比較結果由該些訊號發射元件選擇其中之一者做為目標訊號發射元件;以及經由控制器根據目標訊號發射元件之回波訊號產生量測結果。An embodiment of the present disclosure provides a method for controlling an ultrasonic probe, which includes the following steps: sequentially driving a plurality of signal transmitting elements at a transmitting end through a controller, and each signal transmitting element has an included angle with a signal receiving element at a receiving end, And the angles between the signal transmitting elements and the signal receiving elements are different from each other; the signal receiving elements receive the echo signals of each signal transmitting element and send them to the controller; the controller compares the echo signals and according to the comparison result One of the signal transmitting elements is selected as the target signal transmitting element; and the measurement result is generated by the controller according to the echo signal of the target signal transmitting element.
以下將參照相關圖式,說明依本揭露之超音波探頭及超音波探頭控制方法之實施例,為了清楚與方便圖式說明之故,圖式中的各部件在尺寸與比例上可能會被誇大或縮小地呈現。在以下描述及/或申請專利範圍中,當提及元件「連接」或「耦合」至另一元件時,其可直接連接或耦合至該另一元件或可存在介入元件;而當提及元件「直接連接」或「直接耦合」至另一元件時,不存在介入元件,用於描述元件或層之間之關係之其他字詞應以相同方式解釋。為使便於理解,下述實施例中之相同元件係以相同之符號標示來說明。The following will describe the embodiments of the ultrasonic probe and the method for controlling the ultrasonic probe according to the present disclosure with reference to the related drawings. For the sake of clarity and convenience of the description of the drawings, the components and parts in the drawings may be exaggerated in size and proportion Or present it in a reduced size. In the following description and/or patent application, when an element is referred to as being "connected" or "coupled" to another element, it may be directly connected or coupled to the other element or intervening elements may be present; and when the element is mentioned When "directly connected" or "directly coupled" to another element, there are no intervening elements, and other words used to describe the relationship between the elements or layers should be interpreted in the same manner. For ease of understanding, the same elements in the following embodiments are described with the same symbols.
請參閱第1圖及第2圖,其係為本揭露之第一實施例之超音波探頭之立體圖及側視圖。如第1圖所示,超音波探頭1包含基板10、發射端11及接收端12。Please refer to FIG. 1 and FIG. 2, which are a perspective view and a side view of the ultrasonic probe of the first embodiment disclosed. As shown in FIG. 1, the
發射端11設置於基板10上,並包含二個訊號發射元件111a及111b;在本實施例中,該些訊號發射元件111a及111b可為聲音發射元件,如壓電片等;此類聲音發射元件發出的訊號為放射狀的聲波,其適用於生醫訊號量測,而此類聲音發射元件發出的訊號之頻率範圍較佳的為1~3MHz;其中,低頻率的訊號穿透率高,而高頻率的訊號穿透率低;因此,若應用於生醫訊號量測應用上(如量測胎兒心音或患者之血管深度),此類聲音發射元件發出的訊號之頻率可約為2MHz。The transmitting
在另一實施例中,該些訊號發射元件111a及111b可為光發射元件,如LED光發射器、雷射光發射器等;此類聲音發射元件發出的訊號為直線的光束(較佳的為綠光),其適用於其它類型的訊號量測(非生醫訊號量測)。In another embodiment, the
接收端12設置於基板10上,包含訊號接收元件121;在本實施例中,訊號接收元件121為聲音感測元件,如壓電片等,其適用於生醫量測。The receiving
同樣的,在另一實施例中,訊號接收元件121可為光感測元件,如LED光接收器、雷射光接收器等,其適用於其它類型的訊號量測(非生醫訊號量測)。Similarly, in another embodiment, the
如第2圖所示,訊號發射元件111a與訊號接收元件121之間具有夾角θ1
;訊號發射元件111b與訊號接收元件121之間具有夾角θ2
。As shown in FIG. 2, the
訊號發射元件111b與訊號接收元件121之間的夾角θ2
大於訊號發射元件211a與訊號接收元件121之間的夾角θ1
。The angle θ 2 between the
一般而言,夾角θ1 及夾角θ2 約為1°~20°之間,而夾角θ2 及夾角θ1 之間的差距約為3°~4°;例如,在本實施例中,夾角θ1 可為5°,而夾角θ2 可為8°;在另一實施例中,夾角θ1 可為6°,而夾角θ2 可為10°;夾角θ1 及夾角θ2 可依目標物G之特性進行設計,以獲得最佳的量測結果。Generally speaking, the included angle θ 1 and the included angle θ 2 are between approximately 1° and 20°, and the difference between the included angle θ 2 and the included angle θ 1 is approximately 3° to 4°; for example, in this embodiment, the included angle θ 1 may be 5°, and the included angle θ 2 may be 8°; in another embodiment, the included angle θ 1 may be 6°, and the included angle θ 2 may be 10°; the included angle θ 1 and the included angle θ 2 may be dependent on the target The characteristics of object G are designed to obtain the best measurement results.
請參閱第3圖,其係為本揭露之第一實施例之超音波探頭之運作原理之示意圖。第3圖以訊號發射元件111a為例,以說明超音波探頭1之運作原理。Please refer to FIG. 3, which is a schematic diagram of the operation principle of the ultrasonic probe of the first embodiment disclosed. FIG. 3 uses the
訊號發射元件111a發射超音波訊號US1至目標物G,並由目標物G反射產生回波訊號ES1。The
訊號接收元件121接收回波訊號ES1。The
聲音在空氣中的傳播速度與溫度有關,如下式(1)所示:The speed of sound propagation in the air is related to temperature, as shown in the following formula (1):
v=331+0.6T………………………………………………………...(1)v=331+0.6T...............................................................(1)
其中,v表示聲音在空氣中的傳播速度(m/s);T表示溫度(°C)。Among them, v represents the speed of sound propagation in the air (m/s); T represents the temperature (°C).
而回波訊號ES1由目標物G傳遞至訊號接收元件121之路徑長度可由下式(2)表示:The path length of the echo signal ES1 transmitted from the target G to the
D=v(△t/2)….…………………………………………..…………..(2)D=v(△t/2)........................................................................... (2)
其中,D表示回波訊號ES1由目標物G傳遞至訊號接收元件121之路徑長度(m);△t表示超音波訊號US1由訊號發射元件111發射到訊號接收元件121接收到回波訊號ES1之間的時間(s)。Among them, D represents the path length (m) of the echo signal ES1 from the target G to the
因此,超音波探頭1與目標物G之間的距離可由下式(3)表示:Therefore, the distance between the
X=DcosA = v(△t/2)cosA……………………………..……………(3)X=DcosA = v(△t/2)cosA.........................................................(3)
其中,X表示超音波探頭1與目標物G之間的距離(m);A表示超音波訊號US的入射角。Among them, X represents the distance (m) between the
因此,透過上述的方式,超音波探頭1則可根據回波訊號ES計算超音波探頭1與目標物G之間的距離X。Therefore, in the above manner, the
請參閱第4圖,其係為本揭露之第一實施例之超音波探頭之第一示意圖。如圖所示,由於該些訊號發射元件111a、111b與訊號接收元件121之間的夾角彼此不同,因此可量測不同的距離或深度的待測物。Please refer to FIG. 4, which is a first schematic diagram of the ultrasonic probe of the first embodiment disclosed. As shown in the figure, since the angles between the
訊號發射元件111a發射超音波訊號US1至目標物G,超音波訊號US1由反射面S1反射後產生回波訊號ES1,並傳送至訊號接收元件121。The signal transmitting
訊號發射元件111b發射超音波訊號US2至目標物G,超音波訊號US2由反射面S2反射後產生回波訊號ES2,並傳送至訊號接收元件121。The
根據訊號發射元件111a與訊號接收元件121之間的夾角θ1
,可計算出超音波探頭1與反射面S1之間的距離為M1,而根據訊號發射元件111b與訊號接收元件121之間的夾角θ2
,可計算出超音波探頭1與反射面S2之間的距離為M2;其中,超音波探頭1與反射面S1之間的距離M1可透過下式(4)計算:According to the angle θ 1 between the
tanθ1 =T/M1………………………………………………………..(4)tanθ 1 =T/M1…………………………………………………………..(4)
其中,T表示訊號發射元件111a之中心與訊號接收元件121之中心之間的距離。例如,根據式(4),若θ1
為5°,T為10.5mm,根據式(4)計算可得M1為120mm;若θ1
為5°,T為7.5mm,根據式(4)計算可得M1為86mm。Where, T represents the distance between the center of the
同樣的,超音波探頭1與反射面S2之距離M2可透過下式(5)計算:Similarly, the distance M2 between the
Tanθ2 =T/M2…………...…………………………………………..(5)Tanθ 2 =T/M2........................................................................(5)
其中,T表示訊號發射元件111b之中心與訊號接收元件121之中心之間的距離(在本實施例中,訊號發射元件111a之中心與訊號接收元件121之中心之間的距離與訊號發射元件111b之中心與訊號接收元件121之中心之間的距離相等)。例如,根據式(5),若θ2
為8°,T為10.5mm,根據式(5)計算可得M2為75mm;若θ1
為8°,T為7.5mm,根據式(5)計算可得M2為53mm。Where T represents the distance between the center of the
因此,透過超音波探頭1特殊的結構設計,使超音波探頭1可以有效地量測不同的距離或深度的待測物,因此可以有效地消除偵測盲區,使超音波探頭1的效能大幅提升,故很適合應用於倒車雷達及其它一般性的應用;除此之外,超音波探頭1更可根據都卜勒效應(Doppler effect)有效地量測血流速度。Therefore, through the special structural design of the
請參閱第5圖,其係為本揭露之第一實施例之超音波探頭之第二示意圖。如圖所示,超音波探頭1發射超音波訊號US至血管B,並接收回波訊號以量測血流速度;其中,根據都卜勒效應,血流速度可由下式(6)表示:Please refer to FIG. 5, which is a second schematic diagram of the ultrasonic probe of the first embodiment disclosed. As shown in the figure, the
Vb = (FD × C) / (2FO × Cosα)………………………..……………..(6)V b = (F D × C) / (2F O × Cosα)...............................................................(6)
其中,Vb 表示血流速度;FD 表示都卜勒偏移(Doppler shift);C表示聲音在組織中的速度;FO 表示超音波訊號US的原始頻率;α表示超音波訊號US之波束W與血流方向BD之夾角。由於都卜勒偏移FD 發生二次,故超音波訊號US的原始頻率FO 需要乘以2,而Cosα則用於補償超音波訊號US之波束W與血流方向BD之夾角α。Among them, V b represents the blood flow velocity; F D represents the Doppler shift (Doppler shift); C represents the speed of sound in the tissue; F O represents the original frequency of the ultrasound signal US; α represents the beam of the ultrasound signal US The angle between W and the direction of blood flow BD. Since the Doppler shift F D occurs twice, the original frequency F O of the ultrasonic signal US needs to be multiplied by 2, and Cosα is used to compensate the angle α between the beam W of the ultrasonic signal US and the blood flow direction BD.
透過式(6),超音波探頭1則可根據都卜勒效應(Doppler effect)有效地量測血流速度。Through the formula (6), the
而如前述,本實施例之超音波探頭1具有特殊的結構設計,故若第4圖之目標物G為血管,超音波探頭1也可有效量測不同深度的血管,因此即使不同患者可能有不同的血管深度,超音波探頭1仍可準確地根據都卜勒效應量測這些患者的血流速度,並進一步根據血流速度提供多種數據;例如,心臟排出量(Stroke volume)、心臟排出量指數(Stroke volume index)、心臟排出量變率(Stroke volume variability)、心搏做功(Stroke work)、心臟輸出量(Cardiac output)、心臟指數(Cardiac index)、心臟收縮力(Cardiac power)、血壓(Blood pressure)、心跳(Heart rate)、血流速度峰值(Peak velocity flow)、血流速度時間積分(Velocity time integral)、分鐘距離(Minute distance)、射血時間百分率(Ejection time percent)、全身血管阻力(Systemic vascular resistance)、全身血管阻力指數(Systemic vascular resistance index)、平均壓力差(Mean pressure gradient)、流動時間(Flow time)及流動時間校正(Flow time corrected)等等;超音波探頭2也可應用於其它醫學上的應用。As mentioned above, the
當然,上述僅為舉例,超音波探頭1之結構及元件之間的協同關係均可依實際需求變化,本揭露並不以此為限。Of course, the above is only an example, the structure of the
值得一提的是,現有之超音波探頭由於結構上的限制,使其只能有效量測特定距離範圍的目標物,故當超音波探頭與目標物之距離改變、過近或過深時,超音波探頭容易有偵測盲區,因此無法有效地量測超音波探頭與目標物之間的距離。相反的,根據本揭露之實施例,超音波探頭1之發射端11之包含複數個訊號發射元件111a、111b,且該些訊號發射元件111a、111b與接收端12之訊號接收元件121之間的夾角θ1
、θ2
彼此不同,因此可以有效地量測不同的距離或深度的目標物G,且可精確地量測近距離的目標物G,以消除偵測盲區。It is worth mentioning that due to the structural limitations of the existing ultrasonic probe, it can only effectively measure the target object in a specific distance range, so when the distance between the ultrasonic probe and the target object changes, is too close or too deep, Ultrasonic probes are prone to detect blind spots, so it is impossible to effectively measure the distance between the ultrasonic probe and the target. On the contrary, according to the embodiment of the present disclosure, the transmitting
另外,由於不同患者可能有不同的體型,故也可能有不同的血管深度,故現有超音波探頭應用於量測血流速度等醫學應用時也無法精確地量測不同病人的血流速度。相反的,根據本揭露之實施例,超音波探頭1具有特殊的結構設計,使超音波探頭1可以有效地量測不同的距離或深度的目標物G,故即使不同患者可能有不同的血管深度,超音波探頭1也可以精確地量測血流速度,故很適合應用於量測血流速度等醫學應用。In addition, because different patients may have different body types, and therefore may have different blood vessel depths, the existing ultrasound probe cannot accurately measure the blood flow velocity of different patients when it is used in measuring blood flow velocity and other medical applications. On the contrary, according to the embodiment of the present disclosure, the
請參閱第6圖及第7圖,其係為本揭露之第二實施例之超音波探頭之立體圖及側視圖。如第6圖所示,超音波探頭2包含基板20、發射端21及接收端22。Please refer to FIG. 6 and FIG. 7, which are a perspective view and a side view of the ultrasonic probe of the second embodiment disclosed. As shown in FIG. 6, the
接收端22設置於基板20上,並包含訊號接收元件221。The receiving
發射端21設置於基板20上;與前述實施例不同的是,發射端21包含三個訊號發射元件211a、211b、211c。The transmitting
如第7圖所示,訊號發射元件211a與訊號接收元件221之間具有夾角θ3
;訊號發射元件211b與訊號接收元件221之間具有夾角θ4
;訊號發射元件211c與訊號接收元件221之間具有夾角θ5
。As shown in FIG. 7, the signal-emitting
訊號發射元件211b與訊號接收元件221之間的夾角θ4
大於訊號發射元件211a與訊號接收元件221之間的夾角θ3
;訊號發射元件211c與訊號接收元件221之間的夾角θ5
大於訊號發射元件211b與訊號接收元件221之間的夾角θ4
。Signal-emitting
同樣的,一般而言,夾角θ3 、夾角θ4 及夾角θ5 約為1°~20°之間;夾角θ4 及夾角θ3 之間的差距及夾角θ5 及夾角θ4 之間的差距約為3°~4°,例如,在本實施例中,夾角θ3 可為3°,夾角θ4 可為6°,而夾角θ5 可為9°;在另一實施例中,夾角θ3 可為5°,夾角θ4 可為9°,而夾角θ5 可為13°;夾角θ3 、夾角θ4 及夾角θ5 可依目標物G之特性進行設計,以獲得最佳的量測結果。Similarly, generally speaking, the included angle θ 3 , included angle θ 4 and included angle θ 5 are between 1° and 20°; the difference between the included angle θ 4 and included angle θ 3 and the included angle θ 5 and included angle θ 4 The gap is about 3°~4°. For example, in this embodiment, the included angle θ 3 may be 3°, the included angle θ 4 may be 6°, and the included angle θ 5 may be 9°; in another embodiment, the included angle The angle θ 3 can be 5°, the angle θ 4 can be 9°, and the angle θ 5 can be 13°; the angle θ 3 , the angle θ 4 and the angle θ 5 can be designed according to the characteristics of the target G to obtain the best Measurement results.
由上述可知,超音波探頭2可增加更多的訊號發射元件,使其可以更有效地量測更多不同的距離或深度的目標物G,以符合實際應用上的需求。It can be seen from the above that the
當然,上述僅為舉例,超音波探頭2之結構及元件之間的協同關係均可依實際需求變化,本揭露並不以此為限。Of course, the above is only an example, the structure of the
請參閱第8圖,其係為本揭露之第三實施例之超音波探頭之方塊圖。如圖所示,同樣的,超音波探頭3包含基板30、發射端31及接收端32。Please refer to FIG. 8, which is a block diagram of the ultrasonic probe of the third embodiment of the disclosure. As shown in the figure, similarly, the ultrasonic probe 3 includes a
接收端32設置於基板30上,並包含訊號接收元件321。發射端31設置於基板30上,並包含複數個訊號發射元件311a、311b、311c。超音波探頭3之結構與前述實施例(如第6圖及第7圖所示)相同,故不在此多加贅述。The receiving
與前述實施例不同的是,超音波探頭3更包含控制器33、接收電路34、類比數位轉換器35、發射電路36及選擇開關37。Unlike the previous embodiment, the ultrasonic probe 3 further includes a
控制器33透過選擇開關37選擇訊號發射元件311a,並透過發射電路36驅動訊號發射元件311a發射超音波訊號US3,而接收電路34由訊號接收元件321接收超音波訊號US3之回波訊號ES3,並透過類比數位轉換器35將回波訊號ES3轉換為數位訊號,控制器33則接收並儲存此數位訊號。The
同樣的,控制器33透過選擇開關37選擇訊號發射元件311b,並透過發射電路36驅動訊號發射元件311b發射超音波訊號US4,而接收電路34由訊號接收元件321接收超音波訊號US4之回波訊號ES4,並透過類比數位轉換器35將回波訊號ES4轉換為數位訊號,控制器33則接收並儲存此數位訊號。Similarly, the
接下來,控制器33透過選擇開關37選擇訊號發射元件311c,並透過發射電路36驅動訊號發射元件311c發射超音波訊號US5,而接收電路34由訊號接收元件321接收超音波訊號US5之回波訊號ES5,並透過類比數位轉換器35將回波訊號ES5轉換為數位訊號,控制器33則接收並儲存此數位訊號。Next, the
然後,控制器33比較該些回波訊號ES3、ES4、ES5之訊號特性;在本實施例中,上述之訊號特性為訊號強度;控制器33比較該些回波訊號ES3、ES4、ES5之訊號強度,並選擇具有最高訊號強度之回波訊號之訊號發射元件做為目標訊號發射元件,並根據目標訊號發射元件之回波訊號產生量測結果。在另一實施例中,上述之訊號特性也可為訊號波形或其它相關的特性。例如,若比較結果顯示訊號發射元件311a之回波訊號ES3具有最高的訊號強度,控制器33則選擇訊號發射元件311a做為目標訊號發射元件,並根據其回波訊號ES3產生量測結果。Then, the
控制器33持續透過選擇開關37切換該些訊號發射元件311a、311b、311c以對目標物進行掃描,並重新由該些訊號發射元件中311a、311b、311c選擇具有最高的訊號強度者做為目標訊號發射元件,使量測結果更為精確。The
透過上述特殊的控制邏輯機制,使超音波探頭3能夠準確地由該些訊號發射元件311a、311b、311c中選擇最適當的訊號發射元件做為目標訊號發射元件,並持續掃描以重新由該些訊號發射元件中311a、311b、311c選擇具有最高的訊號強度者做為目標訊號發射元件,使量測結果能最佳化;因此,當超音波探頭3應用於量測血流速度時,即使不同患者可能有不同的血管深度,超音波探頭3仍能精確地量測血流速度。Through the above-mentioned special control logic mechanism, the ultrasonic probe 3 can accurately select the most appropriate signal transmitting element from the
當然,上述僅為舉例,超音波探頭3之結構及元件之間的協同關係均可依實際需求變化,本揭露並不以此為限。Of course, the above is only an example, the structure of the ultrasonic probe 3 and the synergy between the components can be changed according to actual needs, and the disclosure is not limited to this.
請參閱第9圖,其係為本揭露之第三實施例之超音波探頭控制方法之流程圖。本實施例之超音波探頭3之控制方法包含下列步驟:Please refer to FIG. 9, which is a flowchart of the ultrasonic probe control method of the third embodiment disclosed. The control method of the ultrasonic probe 3 of this embodiment includes the following steps:
步驟S91:利用控制器33透過選擇開關37依序選擇發射端31之複數個訊號發射元件311a、311b、311c,該些訊號發射元件311a、311b、311c與接收端之訊號接收元件321之間具有夾角θ3
、θ4
、θ5
,且該些訊號發射元件311a、311b、311c與訊號接收元件321之間的夾角θ3
、θ4
、θ5
彼此不同。Step S91: The
步驟S92:由控制器33控制發射電路36驅動選擇開關37選擇的訊號發射元件。Step S92: The
步驟S93:利用接收電路34接收該些訊號發射元件311a、311b、311c之回波訊號ES3、ES4、ES5,並傳送至控制器33。Step S93: Use the receiving
步驟S94:由類比數位轉換器35將該些回波訊號ES3、ES4、ES5轉換為數位訊號,再傳送至控制器33。Step S94: The analog-to-
步驟S95:透過控制器33比較該些回波訊號ES3、ES4、ES5之訊號強度並選擇具有最高訊號強度之回波訊號之訊號發射元件做為目標訊號發射元件,並根據目標訊號發射元件之回波訊號產生量測結果。Step S95: Compare the signal strength of the echo signals ES3, ES4, ES5 through the
步驟S96:經由控制器33重覆依序驅動該些訊號發射元件311a、311b、311c以重新由該些訊號發射元件311a、311b、311c中選擇該目標訊號發射元件。Step S96: The
更詳細的說,控制器33先選擇訊號發射元件311a,並控制發射電路36驅動訊號發射元件311a;待接收電路34接收訊號發射元件311a之回波訊號ES3後,由類比數位轉換器35將回波訊號ES3轉換為數位訊號,再傳送至控制器33;接下來,控制器33選擇訊號發射元件311b,並控制發射電路36驅動訊號發射元件311b;待接收電路34接收訊號發射元件311b之回波訊號ES4後,由類比數位轉換器35將回波訊號ES4轉換為數位訊號,再傳送至控制器33;然後,控制器33選擇訊號發射元件311c,並控制發射電路36驅動訊號發射元件311c;待接收電路34接收訊號發射元件311c之回波訊號ES5後,由類比數位轉換器35將回波訊號ES5轉換為數位訊號,再傳送至控制器33;最後,控制器33則進行的比較程序以產生量測結果,並再次根據上述的方式依序驅動該些訊號發射元件311a、311b、311c以重新由該些訊號發射元件311a、311b、311c中選擇具有最高訊號強度者做為目標訊號發射元件。More specifically, the controller 33 first selects the signal transmitting element 311a, and controls the transmitting circuit 36 to drive the signal transmitting element 311a; after the receiving circuit 34 receives the echo signal ES3 of the signal transmitting element 311a, the analog-to-digital converter 35 returns The wave signal ES3 is converted into a digital signal and then transmitted to the controller 33; next, the controller 33 selects the signal transmitting element 311b and controls the transmitting circuit 36 to drive the signal transmitting element 311b; the waiting circuit 34 receives the echo of the signal transmitting element 311b After the signal ES4, the analog-to-digital converter 35 converts the echo signal ES4 into a digital signal and sends it to the controller 33; then, the controller 33 selects the signal transmitting element 311c and controls the transmitting circuit 36 to drive the signal transmitting element 311c; After receiving the echo signal ES5 from the signal transmitting element 311c, the receiving circuit 34 converts the echo signal ES5 into a digital signal by the analog-to-digital converter 35, and then transmits it to the controller 33; finally, the controller 33 performs a comparison procedure to generate Measure the results, and drive the signal emitting elements 311a, 311b, and 311c sequentially according to the above-mentioned method to select the one with the highest signal intensity from the signal emitting elements 311a, 311b, and 311c as the target signal emitting element again.
請參閱第10圖,其係為本揭露之第三實施例之超音波探頭之控制邏輯機制之流程圖。第10圖詳細說明了本實施例之超音波探頭之控制邏輯機制之詳細流程,其包含下列步驟:Please refer to FIG. 10, which is a flowchart of the control logic mechanism of the ultrasonic probe of the third embodiment disclosed. Figure 10 details the detailed flow of the control logic mechanism of the ultrasonic probe of this embodiment, which includes the following steps:
步驟S101:選擇並驅動訊號發射元件311a,並接收及儲存訊號發射元件311a之回波訊號ES3,並進入步驟S102。Step S101: Select and drive the
步驟S102:選擇並驅動訊號發射元件311b,並接收及儲存訊號發射元件311b之回波訊號ES4,並進入步驟S103。Step S102: Select and drive the
步驟S103:選擇並驅動訊號發射元件311c,並接收及儲存訊號發射元件311c之回波訊號ES5,並進入步驟S104。Step S103: Select and drive the
步驟S104:比較該些回波訊號ES3、ES4、ES5之訊號強度,並選擇具有最高訊號強度之回波訊號之訊號發射元件做為目標訊號發射元件,並進入步驟S105。Step S104: Compare the signal strengths of the echo signals ES3, ES4, ES5, and select the signal transmitting element of the echo signal with the highest signal strength as the target signal transmitting element, and go to step S105.
步驟S105:根據目標訊號發射元件之回波訊號產生量測結果,並進入步驟S106。Step S105: Generate a measurement result according to the echo signal of the target signal transmitting element, and proceed to step S106.
步驟S106:是否持續進行掃描?若是,則回到步驟S101;若否,則進入步驟S107。Step S106: Do you continue to scan? If yes, go back to step S101; if no, go to step S107.
步驟S107:掃描結束。Step S107: Scanning ends.
當然,上述僅為舉例,超音波探頭1之控制邏輯機制可依實際需求變化,本揭露並不以此為限。Of course, the above is only an example, the control logic mechanism of the
請參閱第11A圖、第11B圖及第11C圖,其係為本揭露之第三實施例之超音波探頭之量測結果圖。第11A圖、第11B圖及第11C圖為應用本揭露之第三實施例之超音波探頭3實際量測目標物G之量測結果圖。Please refer to FIG. 11A, FIG. 11B and FIG. 11C, which are measurement results of the ultrasonic probe of the third embodiment of the disclosure. FIGS. 11A, 11B, and 11C are graphs of measurement results of the actual measurement of the target G using the ultrasonic probe 3 of the third embodiment of the present disclosure.
首先,控制器33依序選擇並驅動訊號發射元件311a、訊號發射元件311b及訊號發射元件311c,而接收電路34分別接收訊號發射元件311a之回波訊號ES3、訊號發射元件311b之回波訊號ES4及訊號發射元件311c之回波訊號ES5。First, the
第11A圖所示為回波訊號ES3之波形,其中橫軸為時間(秒),縱軸為強度,此強度為正規化後的電壓值(伏特);由回波訊號ES3之中間區域的波形可看出,回波訊號ES3有明顯的變化,可視為回波訊號ES3具有較強訊號強度(對比回波訊號ES4、ES5),故訊號發射元件311a能有效地量測到目標物G。Figure 11A shows the waveform of the echo signal ES3, where the horizontal axis is time (seconds) and the vertical axis is intensity. This intensity is the normalized voltage value (volts); the waveform in the middle region of the echo signal ES3 It can be seen that the echo signal ES3 has obvious changes, which can be regarded as that the echo signal ES3 has a stronger signal strength (compared to the echo signals ES4 and ES5), so the
第11B圖所示為回波訊號ES4之波形,其中橫軸為時間,縱軸為強度;由回波訊號ES4之中間區域的波形可看出,回波訊號ES4為零,故訊號發射元件311b無法有效地量測到目標物G。Figure 11B shows the waveform of the echo signal ES4, where the horizontal axis is time and the vertical axis is intensity; as can be seen from the waveform in the middle region of the echo signal ES4, the echo signal ES4 is zero, so the
第11C圖所示為回波訊號ES5之波形,其中橫軸為時間,縱軸為強度;由回波訊號ES5之中間區域的波形可看出,回波訊號ES5為零,故訊號發射元件311c無法有效地量測到目標物G。Figure 11C shows the waveform of the echo signal ES5, where the horizontal axis is time and the vertical axis is intensity; from the waveform of the middle area of the echo signal ES5, it can be seen that the echo signal ES5 is zero, so the
由於訊號發射元件311a能有效地量測到目標物G,故控制器33採用訊號發射元件311a做為目標訊號發射元件,並持續重覆上述步驟,再視訊號發射元件311a、訊號發射元件311b及訊號發射元件311c之量測結果重新由該些訊號發射元件311a、311b、311c中選擇目標訊號發射元件。Since the
綜上所述,根據本揭露之實施例,超音波探頭3之發射端31之包含複數個訊號發射元件311a、311b、311c,且該些訊號發射元件311a、311b、311c與接收端32之訊號接收元件321之間的夾角θ3
、θ4
、θ5
彼此不同,因此可以有效地量測不同的距離或深度的目標物G,且可精確地量測近距離的目標物G,以消除偵測盲區。In summary, according to the embodiment of the present disclosure, the transmitting
又,根據本揭露之實施例,超音波探頭3具有特殊的結構設計,使超音波探頭3可以有效地量測不同的距離或深度的目標物G,故即使不同患者可能有不同的血管深度,超音波探頭3也可以精確地量測血流速度,故很適合應用於量測血流速度等醫學應用。Moreover, according to the embodiment of the present disclosure, the ultrasonic probe 3 has a special structural design, so that the ultrasonic probe 3 can effectively measure the target G at different distances or depths, so even if different patients may have different blood vessel depths, The ultrasonic probe 3 can also accurately measure blood flow velocity, so it is very suitable for medical applications such as measuring blood flow velocity.
此外,根據本揭露之實施例,超音波探頭3具有特殊的控制邏輯機制,使超音波探頭3能夠準確地由該些訊號發射元件311a、311b、311c中選擇最適當的訊號發射元件做為目標訊號發射元件,故可使量測結果更為精確。In addition, according to the embodiment of the present disclosure, the ultrasonic probe 3 has a special control logic mechanism, so that the ultrasonic probe 3 can accurately select the most appropriate signal transmitting element from the
可見本揭露在突破先前之技術下,確實已達到所欲增進之功效,且也非熟悉該項技藝者所易於思及,其所具之進步性、實用性,顯已符合專利之申請要件,爰依法提出專利申請,懇請 貴局核准本件專利申請案,以勵創作,至感德便。It can be seen that this disclosure has indeed achieved the desired effect by breaking through the previous technology, and it is not easy to think about by those who are familiar with this art. Its progressiveness and practicality have obviously met the patent application requirements. I filed a patent application in accordance with the law, and urge your office to approve this patent application in order to encourage creation and to feel virtuous.
以上所述僅為舉例性,而非為限制性者。其它任何未脫離本揭露之精神與範疇,而對其進行之等效修改或變更,均應該包含於後附之申請專利範圍中。The above is only exemplary, and not restrictive. Any other equivalent modifications or changes made without departing from the spirit and scope of this disclosure should be included in the scope of the attached patent application.
1、2、3‧‧‧超音波探頭US、US1~US5‧‧‧超音波訊號10、20、30‧‧‧基板ES、ES1~ES5‧‧‧回波訊號11、21、31‧‧‧發射端G‧‧‧目標物111a、111b、111c、211a、211b、211c、311a、311b、311c‧‧‧訊號發射元件S1、S2‧‧‧反射面12、22、23‧‧‧接收端B‧‧‧血管121、221、321‧‧‧訊號接收元件W‧‧‧波束33‧‧‧控制器A‧‧‧入射角34‧‧‧接收電路X、T‧‧‧距離35‧‧‧類比數位轉換器D‧‧‧路徑長度36‧‧‧發射電路BD‧‧‧血流方向37‧‧‧選擇開關α‧‧‧夾角θ1、θ2、θ3、θ4、θ5、α‧‧‧夾角S91~S96、S101~S107‧‧‧步驟流程1, 2, 3‧‧‧Ultrasonic probe US, US1~US5‧‧‧
第1圖 係為現有之超音波探頭之示意圖。Figure 1 is a schematic diagram of an existing ultrasonic probe.
第2圖 係為本揭露之第一實施例之超音波探頭之立體圖。FIG. 2 is a perspective view of the ultrasonic probe of the first embodiment disclosed.
第3圖 係為本揭露之第一實施例之超音波探頭之側視圖。FIG. 3 is a side view of the ultrasonic probe of the first embodiment disclosed.
第4圖 係為本揭露之第一實施例之超音波探頭之第一示意圖。FIG. 4 is a first schematic diagram of the ultrasonic probe of the first embodiment disclosed.
第5圖 係為本揭露之第一實施例之超音波探頭之第二示意圖。FIG. 5 is a second schematic diagram of the ultrasonic probe of the first embodiment disclosed.
第6圖 係為本揭露之第二實施例之超音波探頭之立體圖。FIG. 6 is a perspective view of the ultrasonic probe of the second embodiment disclosed.
第7圖 係為本揭露之第二實施例之超音波探頭之側視圖。FIG. 7 is a side view of the ultrasonic probe of the second embodiment disclosed.
第8圖 係為本揭露之第三實施例之超音波探頭之方塊圖。FIG. 8 is a block diagram of the ultrasonic probe of the third embodiment disclosed.
第9圖 係為本揭露之第三實施例之超音波探頭控制方法之流程圖。FIG. 9 is a flowchart of the ultrasonic probe control method of the third embodiment disclosed.
第10圖 係為本揭露之第三實施例之超音波探頭之控制邏輯機制之流程圖。FIG. 10 is a flowchart of the control logic mechanism of the ultrasonic probe of the third embodiment disclosed.
第11A圖、第11B圖及第11C圖 係為本揭露之第三實施例之超音波探頭之量測結果圖。Figures 11A, 11B, and 11C are measurement results of the ultrasonic probe of the third embodiment of the disclosure.
1‧‧‧超音波探頭 1‧‧‧Ultrasonic probe
10‧‧‧基板 10‧‧‧ substrate
11‧‧‧發射端 11‧‧‧ Launcher
111a、111b‧‧‧訊號發射元件 111a, 111b ‧‧‧ signal transmitting element
12‧‧‧接收端 12‧‧‧Receiver
121‧‧‧訊號接收元件 121‧‧‧Signal receiving component
θ1、θ2‧‧‧夾角 θ 1 , θ 2 ‧‧‧ included angle
Claims (17)
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Citations (1)
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US4821575A (en) * | 1986-10-06 | 1989-04-18 | Nippon Steel Corporation | Ultrasonic flaw detecting method and apparatus |
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US4821575A (en) * | 1986-10-06 | 1989-04-18 | Nippon Steel Corporation | Ultrasonic flaw detecting method and apparatus |
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